Patent Application
20150094914
The present invention includes support and sensing structures positioned in a physiologic tunnel for measuring bodily functions and to manage abnormal conditions indicated by the measurements.
Interfering constituents and variables can introduce significant source of errors that prevent measured biologic parameters from being of clinical value. In order to bypass said interfering constituents and achieve undisturbed signals, invasive and semi-invasive techniques have been used. Such techniques have many drawbacks including difficulties in providing continuous monitoring for long periods of time. Non-invasive techniques also failed to deliver the clinical usefulness needed. The placement of a sensor on the skin characterized by the presence of interfering constituents do not allow obtaining clinically useful nor accurate signals due to the presence of said interfering constituents and background noise which greatly exceeds the signal related to the physiologic parameter being measured.
The most precise, accurate, and clinically useful way of evaluating thermal status of the body in humans and animals is by measuring brain temperature. Brain temperature measurement is the key and universal indicator of both disease and health equally, and is the only vital sign that cannot be artificially changed by emotional states. The other vital signs (heart rate, blood pressure, and respiratory rate) all can be influenced and artificially changed by emotional states or voluntary effort.
Body temperature is determined by the temperature of blood, which emits heat as far-infrared radiation. Adipose tissue (fat tissue) absorbs far-infrared and the body is virtually completely protected with a layer of adipose tissue adherent to the skin. Thus measurement of temperature using the skin did not achieve precision nor accuracy because previous techniques used sensors placed on skin characterized by the presence of adipose tissue.
Because it appeared to be impossible with current technology to non-invasively measure brain temperature, attempts were made to determine internal body temperature, also referred to as core temperature. An invasive, artificial, inconvenient, and costly process is currently used to measure internal (core) temperature consisting of inserting a catheter with a temperature sensor in the urinary canal, rectum or esophagus. But such methodology is not suitable for routine measurement, it is painful, and has potential fatal complications.
Semi-invasive techniques have also being tried. Abreu disclosed in U.S. Pat. No. 6,120,460 apparatus and methods for measuring core temperature continuously using a contact lens in the eyelid pocket, but the contact lens is a semi-invasive device which requires prescription by a physician and sometimes it is not easy to place the contact lens in the eye of an infant or even in adults and many people are afraid of touching their eyes.
There are several drawbacks and limitations in the prior art for continuous and/or core measurement of temperature.
Measurement of temperature today is non-continuous, non-core and nurse dependent. Nurses have to stick a thermometer in the patient's mouth, rectum or ear. To get core temperature nurses invasively place a tube inside the body which can cause infection and costly complications.
Measurement of core temperature on a routine basis in the hospital and/or continuously is very difficult and risky because it requires an invasive procedure with insertion of tubes inside the body or by ingesting a thermometer pill. The thermometer pill can cause diarrhea, measure temperature of the fluid/food ingested and not body temperature, and have fatal complications if the pill obstructs the pancreas or liver ducts. Placement of sensors on the skin do not provide clinically useful measurements because of the presence of many interfering constituents including fat tissue.
It is not possible to acquire precise and clinically useful measurements of not only brain temperature, but also metabolic parameters, physical parameters, chemical parameters, and the like by simply placing a sensor on the skin. One key element is the presence of fat tissue. Fat varies from person to person, fat varies with aging, fat content varies from time to time in the same person, fat attenuates a signal coming from a blood vessel, fat absorbs heat, fat prevents delivery of undisturbed far-infrared radiation, fat increases the distance traveled by the element being measured inside the body and an external sensor placed on the surface of the skin.
There is a need to identify a method and apparatus that can non-invasively, conveniently and continuously monitor brain temperature in a painless, simple, external and safe manner with sensors placed on the skin.
There is further a need to identify a method and apparatus that can conveniently, non-invasively, safely and precisely monitor biological parameters including metabolic parameters, physical parameters, chemical parameters, and the like.
There is a need to identify an apparatus and method capable of measuring biological parameters by positioning a sensor on a physiologic tunnel for the acquisition of undisturbed and continuous biological signals.
The present invention provides methods, apparatus and systems that effectively address the needs of the prior art.
In general, the invention provides a set of sensing systems and reporting means which may be used individually or in combination, which are designed to access a physiologic tunnel to measure biological, physical and chemical parameters. Anatomically and physiologically speaking, the tunnel discovered by the present invention is an anatomic path which conveys undisturbed physiologic signals to the exterior. The tunnel consists of a direct and undisturbed connection between the source of the function (signal) within the body and an external point at the end of the tunnel located on the skin. A physiologic tunnel conveys continuous and integral data on the physiology of the body. An undisturbed signal from within the body is delivered to an external point at the end of the tunnel. A sensor placed on the skin at the end of the tunnel allows optimal signal acquisition without interfering constituents and sources of error.
Included in the present invention are support structures for positioning a sensor on the skin at the end of the tunnel. The present invention discloses devices directed at measuring brain temperature, brain function, metabolic function, hydrodynamic function, hydration status, hemodynamic function, body chemistry and the like. The components include devices and methods for evaluating biological parameters using patches, clips, eyeglasses, head mounted gear and the like with sensing systems adapted to access physiologic tunnels to provide precise and clinically useful information about the physiologic status of the wearer and for enhancing the safety and performance of said wearer, and helping to enhance and preserve the life of said wearer by providing adequate reporting means and alert means relating to the biological parameter being monitored. Other components provide for producing direct or indirect actions, acting on another device, or adjusting another device or article of manufacture based on the biological parameter measured.
The search for a better way to measure biological parameters has resulted in long and careful research, which included the discovery of a Brain Temperature Tunnel (BTT) and other physiologic tunnels in humans and animals. The present invention was the first to recognize the physiologic tunnel in the body. The present invention was yet the first to recognize the end of the tunnel on the skin surface in which an optimal signal is acquired and measurements can be done without the presence of interfering constituents and background noise that exceeds the signal being measured. The present invention was also the first to recognize and precisely map the special geometry and location of the tunnel including the main entry point. The present invention was yet first to recognize the precise positioning of sensing systems at the main entry point for optimal signal acquisition. Careful studies have been undertaken including software development for characterizing infrared radiation to precisely determine the different aspects of the tunnel. This research has determined that the measurement of brain (core) temperature and other body parameters can be accomplished in a non-invasive and continuous manner in humans and animals with sensors positioned in a confined area of the skin at the end of a physiologic tunnel.
The key function and critical factor for life preservation and human performance is brain temperature. Brain tissue is the tissue in the body most susceptible to thermal damage, by both high and low temperature. Brain temperature is the most clinically relevant parameter to determine the thermal status of the body and the human brain is responsible for 18 to 20% of the heat produced in the body, which is an extraordinary fact considering that the brain represents only 2% of the body weight. The great amount of thermal energy generated in the brain is kept in a confined space and the scalp, skull, fat and CSF (cerebral spinal fluid) form an insulating layer. The recognition of the BTT by the present invention bypasses the insulating barriers and provides a direct connection to inside the brain physiology and physics.
Anatomically and physiologically speaking, a Brain Temperature Tunnel consists of a continuous, direct, and undisturbed connection between the heat source within the brain and an external point at the end of the tunnel. The physical and physiological events at one end of the tunnel inside the brain are reproduced at the opposite end on the skin. A BTT enables the integral and direct heat transfer through the tunnel without interference by heat absorbing elements, i.e., elements that can absorb far-infrared radiation transmitted as heat by blood within the brain. There are six characteristics needed to define a BTT. These characteristics are: 1) area without heat absorbing elements, i.e., the area must not contain adipose tissue (fat tissue). This is a key and needed characteristic for defining a temperature tunnel, 2) area must have a terminal branch of a vessel in order to deliver the integral amount of heat, 3) terminal branch has to be a direct branch of a blood vessel from the brain, 4) terminal branch has to be superficially located to avoid heat absorption by deep structures such as muscles, 5) area must have a thin and negligible interface between a sensor and the source of thermal energy to achieve high heat flow, and 6) area must not have thermoregulatory arteriovenous shunts. All six characteristics are present on the skin on the medial canthal area adjacent to the medial corner of the eye above the medial canthal tendon and in the medial third of the upper eyelid. In more detail the end of BTT area on the skin measures about 11 mm in diameter measured from the medial corner of the eye at the medial canthal tendon and extends superiorly for about 6 mm and then extends into the upper eyelid in a horn like projection for another 22 mm.
The BTT area is the only area in the body without adipose tissue, which is in addition supplied by a terminal branch, which has a superficial blood vessel coming from the brain vasculature, and which has a thin interface and no thermoregulatory shunts. The BTT area is supplied by a terminal branch of the superior ophthalmic vein which is a direct connection to the cavernous sinus, said cavernous sinus being an endothelium-lined system of venous channels inside the brain which collects and stores thermal energy. The blood vessel supplying the BTT area is void of thermoregulatory arteriovenous shunts and it ends on the skin adjacent to the medial corner of the eye and in the superior aspect of the medial canthal area right at the beginning of the upper eyelid. The blood vessels deliver undisturbed heat to the skin on the medial canthal area and upper eyelid as can be seen in the color as well as black and white photos of infrared images shown in
If the blood vessel is located deep, other tissues and chemical substances would absorb the heat, and that can invalidate the clinical usefulness of the measurement. There is direct heat transfer and the skin in the BTT area is the thinnest skin in the body and is void of thermoregulatory arteriovenous shunts. A very important aspect for optimal measurement of temperature is no interference by fat tissue and direct heat transfer.
The absence of fat tissue in this particular and unique area in the body at the end of the tunnel allows the undisturbed acquisition of the signal. The combination of those six elements allows the undisturbed and integral emission of infrared radiation from the brain in the form of direct heat transfer at the BTT area location, which can be seen in the infrared image photographs (
From a physical standpoint, the BTT is the equivalent of a Brain Thermal Energy tunnel with high total radiant power and high heat flow. The temperature of the brain is determined by the balance between thermal energy produced due to metabolic rate plus the thermal energy delivered by the arterial supply to the brain minus the heat that is removed by cerebral blood flow. Convection of heat between tissue and capillaries is high and the temperature of the cerebral venous blood is in equilibrium with cerebral tissue. Accordingly, parenchymal temperature and thermal energy of the brain can be evaluated by measuring the temperature and thermal energy of the cerebral venous blood. The superior ophthalmic vein has a direct and undisturbed connection to the cavernous sinus and carries cerebral venous blood with a thermal energy capacity of 3.6 Jml.sup.−1(.degree. C.).sup.−1 at hematocrit of 45%. Cerebral thermodynamic response, thermal energy, and brain temperature can be evaluated by placing a sensor to capture thermal energy conveyed by the cerebral venous blood at the end of the BTT.
The research concerning BTT and physiologic tunnels involved various activities and studies including: 1) In-vitro histologic analysis of mucosal and superficial body areas; 2) In-vivo studies with temperature evaluation of external areas in humans and animals; 3) In-vivo functional angiographic evaluation of heat source; 4) Morphologic studies of the histomorphometric features of the BTT area; 5) In-vivo evaluation of temperature in the BTT area using: thermocouples, thermistors, and far-infrared; 6) Comparison of the BTT area measurements with the internal eye anatomy and current standard most used (oral) for temperature measurement; 7) Cold and heat challenge to determine temperature stability of BTT; and 8) Infrared imaging and isotherm determination. Software for evaluating geometry of tunnel was also developed and used. Simultaneous measurement of a reference temperature and temperature in the BTT area were done using pre-equally calibrated thermistors. A specific circuit with multiple channels was designed for the experiments and data collection.
The measurement of temperature in the BTT area showed almost identical temperature signal between the BTT area and the internal conjunctival anatomy of the eye, which is a continuation of the central nervous system. Measurement of the temperature in the internal conjunctival anatomy of eye as used in the experiment was described by Abreu in U.S. Pat. Nos. 6,120,460 and 6,312,393. The averaged temperature levels for BTT and internal eye were within 0.1.degree. C. (0.18.degree. F.) with an average normothermia value equivalent of 37.1.degree. C. (98.8.degree. F.) for the BTT and 37.degree. C. (98.6.degree. F.) for the internal eye. Comparison with the standard most used, oral temperature, was also performed. The temperature voltage signal of the BTT area showed an average higher temperature level in the BTT area of an equivalent of 0.3.degree. C. (0.5.degree. F.) when compared to oral.
Subjects underwent cold challenge and heat challenge through exercising and heat room. The lowering and rising of temperature in the BTT area was proportional to the lowering and rising in the oral cavity. However, the rate of temperature change was faster in the BTT area than for oral by about 1.2 minutes, and temperature at the BTT site was 0.5.degree. C. (0.9.degree. F.) higher on few occasions. Subjects of different race, gender, and age were evaluated to determine the precise location of the BTT area across a different population and identify any anatomic variation. The location of the BTT was present at the same location in all subjects with no significant anatomic variation, which can be seen in a sample of infrared imaging of different subjects.
The tunnel is located in a crowded anatomic area and thus the positioning of the sensor requires special geometry for optimal alignment with the end of the tunnel. The clinical usefulness of the tunnel can only be achieved with the special positioning of the sensor in relation to anatomic landmarks and the support structure. The tunnel is located in a unique position with distinctive anatomic landmarks that help define the external geometry and location of the end of the tunnel. The main entry point of the tunnel, which is the preferred location for positioning the sensor, requires the sensor to be preferably placed in the outer edge of a support structure. The preferred embodiment for the measurement of biological parameters by accessing a physiologic tunnel includes sensors positioned in a particular geometric position on the support structure.
The support structure includes patches containing sensors. For the purpose of the description any structure containing an adhesive as means to secure said structure to the skin at the end of the tunnel is referred to as a patch including strips with adhesive surfaces such as a “BAND-AID” adhesive bandage. It is understood that a variety of attachment means can be used including adhesives, designs incorporating spring tension pressure attachment, and designs based on other attachment methods such as elastic, rubber, jelly-pads and the like.
The patches are adapted to position sensors at the end of the tunnel for optimal acquisition of the signal. The patch is preferably secured to the area by having an adhesive backing which lays against the skin, although a combination of adhesive and other means for creating a stable apposition of the sensor to the tunnel can be used such as fastening or pressure.
Support structures also include clips or structures that are positioned at the end of the tunnel with or without adhesive and which are secured to the area by pressure means. Any structure that uses pressure means to secure said structure to the skin at the end of the tunnel is referred as a clip.
Head-mounted structures are structures mounted on the head or neck for positioning sensors on the end of the tunnel and include headbands with accessories that are adjacent to the tunnel, visors, helmets, headphone, structures wrapping around the ear and the like. For the purpose of this description TempAlert is referred herein as a system that measures temperature in the BTT area and has means to report the measured value and that can incorporate alarm devices that are activated when certain levels are reached. Support structures yet include any article that has sensing devices in which said sensing devices are positioned at the end of the tunnel.
Support structures further include medial canthal pieces of eyeglasses. A medial canthal piece is also referred to herein as a medial canthal pad and includes a pad or a piece which positions sensing devices on the skin at the medial canthal area on top of a tunnel, with said medial canthal piece being permanently attached to or mounted to an eyeglass. Any sensing devices incorporated in an eyeglass (fixed or removable) for accessing a tunnel are referred to herein as EyEXT including devices for sensing physical and chemical parameters. Any article of manufacture that has visual function, or ocular protection, or face protection with a part in contact with the tunnel is referred herein as eyeglasses and includes conventional eyeglasses, prescription eyeglasses, reading glasses, sunglasses, goggles of any type, masks (including gas masks, surgical masks, cloth masks, diving masks, eyemask for sleeping and the like) safety glasses, and the like.
For brain temperature evaluation the tunnel area consists of the medial canthal area and the superior aspect of the medial corner of the eye. For brain function evaluation the tunnel area consists of primarily the upper eyelid area. For metabolic function evaluation the tunnel area consists of an area adjacent to the medial corner of the eye and both the upper and lower eyelids.
The measurement of metabolic function, brain function, immunogenic function, physical parameters, physico-chemical parameters and the like includes a variety of support structures with sensors accessing the physiologic tunnels. The sensors are placed in apposition to the skin immediately adjacent to the medial corner of the eye preferably in the superior aspect of the medial canthal area. The sensor can also be positioned in the medial third of the upper eyelid. The sensor is most preferably located at the main entry point of the tunnel which is located on the skin 2.5 mm medial to the corner of the eye and about 3 mm above the medial corner of the eye. The diameter of the main entry point is about 6 to 7 mm. The positioning of the sensor at the main entry point of the tunnel provides the optimum site for measuring physical and chemical parameters of the body.
Besides a sensor that makes contact with the skin at the Target Area, it is understood that sensors which do not make contact with the skin can be equally used. For instance an infrared-based temperature measuring system can be used. The measurement is based on the Stefan-Boltzman law of physics in which the total radiation is proportional to the fourth power of the absolute temperature, and the Wien Displacement law in which the product of the peak wavelength and the temperature are constant. The field of view of the non-contact infrared apparatus of the invention is adapted to match the size and geometry of the BTT area on the skin.
A variety of lenses known in the art can be used for achieving the field of view needed for the application. For example, but not by way of limitation, a thermopile can be adapted and positioned in a manner to have a field of view aimed at the main entry point of the BTT area on the skin. The signal is then amplified, converted into a voltage output and digitized by a MCU (microcontroller).
This infrared-based system can be integrated into a support structure that is in contact with the body such as any of the support structures of the present invention. In addition, it is understood that the infrared-based system of the present invention can be integrated as a portable or hand-held unit completely disconnected from the body. The apparatus of the present invention can be held by an operator that aims said apparatus at the BTT area to perform the measurement. The apparatus further includes an extension shaped to be comfortably positioned at the BTT site for measuring biological parameters without discomfort to the subject. The extension in contact with the skin at the BTT is shaped in accordance with the anatomic landmarks and the geometry and size of the BTT site. The infrared radiation sensor is positioned in the extension in contact with the skin for receiving radiation emitted from the BTT site.
The present invention provides a method for measuring biological parameters including the steps of positioning a sensing device means on the skin area at the end of a tunnel, producing a signal corresponding to the biological parameter measured and reporting the value of the parameter measured.
It is also includes a method to measure biological parameters by non-contact infrared thermometry comprising the steps of positioning an infrared detector at the BTT site with a field of view that encompasses the BTT site and producing a signal corresponding to the measured infrared radiation. The biological parameters include temperature, blood chemistry, metabolic function and the like.
Temperature and ability to do chemical analysis of blood components is proportional to blood perfusion. The present invention recognizes that the tunnel area, herein also referred as a Target Area, has the highest superficial blood perfusion in the head and has a direct communication with the brain, and that the blood vessels are direct branches of the cerebral vasculature and void of thermoregulatory arteriovenous shunts. It was also recognized that the Target Area has the highest temperature in the surface of the body as can be seen in the photographs of experiments measuring infrared emission from the body and the eye.
The Target Area discovered not only has the thinnest and most homogeneous skin in the whole body but is the only skin area without a fat layer. Since fat absorbs significant amounts of radiation, there is a significant reduction of signal. Furthermore other skin areas only provide imprecise and inaccurate signals because of the large variation of adipose tissue from person to person and also great variability of fat tissue according to age. This interference by a fat layer does not occur in the Target Area. Furthermore, the combined characteristics of the Target Area, contrary to the skin in the rest of the body, enable the acquisition of accurate signals and a good signal to noise ratio which far exceeds background noise. In addition, body temperature such as is found in the surface of the skin in other parts of the body is variable according to the environment.
Another important discovery of the present invention was the demonstration that the Target Area is not affected by changes in the environment (experiments included cold and heat challenge). The Target Area provides an optimum location for temperature measurement which has a stable temperature and which is resistant to ambient conditions. The Target Area discovered has a direct connection to the brain, is not affected by the environment and provides a natural, complete thermal seal and stable core temperature. The apparatus and methods of the present invention achieve precision and clinical usefulness needed with the non-invasive placement of a temperature sensor on the skin in direct contact with the heat source from the brain without the interference of heat absorbing elements.
The Target Area is extremely vascularized and is the only skin area in which a direct branch of the cerebral vasculature is superficially located and covered by a thin skin without a fat layer. The main trunk of the terminal branch of the ophthalmic vein is located right at the BTT area and just above the medial canthal tendon supplied by the medial palpebral artery and medial orbital vein. The BTT area on the skin supplied by a terminal and superficial blood vessel ending in a particular area without fat and void of thermoregulatory arteriovenous shunts provides a superficial source of undisturbed biological signals including brain temperature, metabolic function, physical signals, and body chemistry such as glucose level, and the like.
Infrared spectroscopy is a technique based on the absorption of infrared radiation by substances with the identification of said substances according to its unique molecular oscillatory pattern depicted as specific resonance absorption peaks in the infrared region of the electromagnetic spectrum. Each chemical substance absorbs infrared radiation in a unique manner and has its own unique absorption spectra depending on its atomic and molecular arrangement and vibrational and rotational oscillatory pattern. This unique absorption spectra allows each chemical substance to basically have its own infrared spectrum, also referred to as fingerprint or signature which can be used to identify each of such substances. Radiation containing various infrared wavelengths is emitted at the substance to be measured and the amount of absorption of radiation is dependent upon the concentration of said chemical substance being measured according to Beer-Lambert's Law.
Interfering constituents and variables such as fat, bone, muscle, ligaments and cartilage introduce significant source of errors which are particularly critical since the background noise greatly exceeds the signal of the substance of interest. Since those interfering constituents are not present on the skin at the BTT area, the sensing systems positioned at said BTT area can acquire optimal signal with minimal noise including spectroscopic-based measurements.
Spectroscopic devices integrated into support structures disclosed in the present invention can precisely non-invasively measure blood components since the main sources of variation and error, such as fat tissue, are not present in the Target Area. In addition, other key constituents which interfere with electromagnetic energy emission such as muscle, cartilage and bones, are not present in the Target Area either. The blood vessels delivering the infrared radiation are superficially located and the infrared radiation is delivered at the end of the tunnel without interacting with other structures. The only structure to be traversed by the infrared radiation is a very thin skin, which does not absorb the infrared wavelength. The present invention includes infrared spectroscopy means to provide a clinically useful measurement with the precise and accurate determination of the concentration of the blood components at the end of the tunnel.
In addition to spectroscopy in which electromagnetic energy is delivered to the Target Area, the present invention also discloses apparatus and methods for measuring substances of interest through far infrared thermal emission from the Target Area. Yet, besides near-infrared spectroscopy and thermal emission, other devices are disclosed for measurement of substances of interest at the Target Area including electroosmosis as a flux enhancement by iontophoresis or reverse iontophoresis with increased passage of fluid through the skin through application of electrical energy. Yet, transcutaneous optical devices can also be integrated into support structures including medial canthal pieces, modified nose pads, and the frame of eyeglasses, with said devices positioned to access the tunnel.
It is understood that application of current, ultrasonic waves as well as chemical enhancers of flow, electroporation and other devices can be used to increase permeation at the tunnel site such as for example increased flow of glucose with the use of alkali salts. In addition creating micro holes in the target area with a laser, or other means that penetrate the skin can be done with the subsequent placement of sensing devices on the BTT site, with said devices capable of measuring chemical compounds. Furthermore, reservoirs mounted on or disposed within support structures, such as the frame and pads of eyeglasses, can deliver substances transdermally at the BTT site by various devices including iontophoresis, sonophoresis, electrocompression, electroporation, chemical or physical permeation enhancers, hydrostatic pressure and the like.
In addition to measure the actual amount of oxygen in blood, the present invention also discloses devices to measure oxygen saturation and the amount of oxygenated hemoglobin. In this embodiment the medial canthal piece of a support structure or the modified nose pads of eyeglasses contain LEDs emitting at two wave lengths around 940 and 660 nanometers. As the blood oxygenation changes, the ratio of the light transmitted by the two frequencies changes indicating the oxygen saturation. Since the blood level is measured at the end of a physiologic brain tunnel, the amount of oxygenated hemoglobin in the arterial blood of the brain is measured, which is the most valuable and key parameter for athletic purposes and health monitoring.
The present invention also provides a method for measuring biological parameters with said method including the steps of directing electromagnetic radiation at the BTT area on the skin, producing a signal corresponding to the resulting radiation and converting the signal into a value of the biological parameter measured.
Besides using passive radio transmission or communication by cable; active radio transmission with active transmitters containing a microminiature battery mounted in the support structure can also be used. Passive transmitters act from energy supplied to it from an external source. The transensor transmits signals to remote locations using different frequencies indicative of the levels of biological parameters. Ultrasonic micro-circuits can also be mounted in the support structure and modulated by sensors which are capable of detecting chemical and physical changes at the Target Area. The signal may be transmitted using modulated sound signals particularly under water because sound is less attenuated by water than are radio waves.
One preferred embodiment comprises a support structure including a patch adapted to be worn on or attached with adhesives to the tunnel and includes structural support, a sensor for measuring biological parameters, power source, microcontroller and transmitter. The parts can be incorporated into one system or work as individual units. The sensor is located preferably within 7 mm from the outer edge of the patch. The apparatus of the invention can include a temperature sensor located in the outer edge of the patch for sensing temperature. The transmitter, power source and other components can be of any size and can be placed in any part of the patch or can be connected to the patch as long as the sensing part is placed on the edge of the patch in accordance with the principles of the invention. The sensor in the patch is positioned on the skin adjacent to the medial canthal area (medial corner of the eye) and located about 2 mm from the medial canthal tendon. The sensor can preferably include electrically-based sensors, but non-electrical systems can be used such as chemicals that respond to changes in temperature including mylar.
Besides patches, another preferred embodiment for measuring biological parameters at the physiologic tunnel includes a medial canthal pad. The medial canthal piece is a specialized structure containing sensors for accessing the tunnel and adapted to be worn on or attached to eyeglasses in apposition to the tunnel and includes structural support, a sensor for measuring biological parameters, power source, microcontroller and transmitter. The parts can be incorporated into one system or work as individual units. The sensors are positioned on the BTT area. The transmitter, power source, and other components can be placed in the medial canthal pad or in any part of the eyeglasses. A medial canthal piece or extension of nose pads of eyeglasses allow accessing the physiologic tunnel with sensing devices laying in apposition to the BTT area.
The apparatus of the invention include a temperature sensor located in the medial canthal pad. For temperature measurement the sensing system is located on a skin area that includes the medial canthal corner of the eye and upper eyelid. The sensor in the medial canthal pad is preferably positioned on the skin adjacent to the medial canthal area (medial corner of the eye). Although one of the preferred embodiments for measurement of brain temperature consists of medial canthal pads, it is understood that also included in the scope of the invention are nose pads of a geometry and size that reach the tunnel and that are equipped with temperature sensors preferably in the outer edge of said nose pads for measuring brain temperature and other functions. An oversized and modified nose pad containing sensors using a special geometry for adequate positioning at the BTT area is also included in the invention.
With the disclosure of the present invention and by using anatomic landmarks in accordance with the invention the sensor can be precisely positioned on the skin at the end of the tunnel. However, since there is no external visible indication on the skin relating to the size or geometry of the tunnel, accessory means can be used to visualize, map or measure the end of the tunnel on the skin. These accessory means may be particularly useful for fitting medial canthal pads or modified nose pads of eyeglasses.
Accordingly, an infrared detector using thermocouple or thermopiles can be used as an accessory for identifying the point of maximum thermal emission and to map the area. An infrared imaging system or thermography system may be preferably used. In this instance, an optical store selling the eyeglasses can have a thermal imaging system. The optician, technician and the like take an infrared image picture or film the area, and in real time localize the tunnel of the particular user. The medial canthal pads or modified nose pads can then be adjusted to fit the particular user based on the thermal infrared imaging. The eyeglasses are fitted based on the thermal image created. This will allow customized fitting according to the individual needs of the user. Any thermography-based system can be used including some with great visual impact and resolution as a tri-dimensional color thermal wave imaging.
It is also a feature of the invention to provide a method to be used for example in optical stores for locating the tunnel including the steps of measuring thermal infrared emission, producing an image based on the infrared emission, and detecting the area with the highest amount of infrared emission. Another step that can be included is adjusting sensors in support structures to match the area of highest infrared emission.
One of said support structures includes the medial canthal pieces or nose pads of eyeglasses. The thermal imaging method can be used for fitting a patch, but said patch can be positioned at the tunnel by having an external indicator for lining up said indicator with a permanent anatomic landmark such as the medial corner of the eye. Although medial canthal pieces of eyeglasses can have an external indicator for precise positioning, since opticians are used to fit eyeglasses according to the anatomy of the user, the thermal imaging method can be a better fit for eyeglasses than an external indicator on the medial canthal pieces or modified nose pads of eyeglasses.
The source of the signal is key for the clinical usefulness of the measurement. The brain is the key and universal indicator of the health status of the body. The signal coming from the brain or brain area provides the most clinically useful data. In accordance with another embodiment, the measurement of biological parameters will be described. The amount of sodium and other elements in sweat is a key factor for safety and performance of athletes and military, as well as health monitoring.
For instance hyponatremia (decreased amount of sodium) can lead to reduced performance and even death. Hyponatremia can occur due to excess water intake, commonly occurring with intense physical activity and military training. Sweat can be considered as an ultrafiltrate of blood. The blood vessels supplying the skin on the head are branches of the central nervous system vasculature. The amount of chemical substances present in the sweat coming from those blood vessels is indicative of the amount of chemical substances present in the cerebral vasculature. For instance, sodium concentration of sweat from blood vessels in the head changes in relation to the rates of sweating. The apparatus and methods of the present invention can prevent death or harm due to water intoxication, by providing alert signals when the levels of sodium in sweat reach a certain threshold for that particular wearer. The presence of various chemical elements, gases, electrolytes and pH of sweat and the surface of the skin can be determined by the use of suitable electrodes and suitable sensors integrated in the eyeglasses and other support structures mounted on the head or fitted on the head or face. These electrodes, preferably microelectrodes, can be sensitized by several reacting chemicals which are in the sweat or the surface of the skin. The different chemicals and substances can diffuse through suitable permeable membranes sensitizing suitable sensors.
For example but not by way of limitation, electrochemical sensors can be used to measure various analytes such as glucose using a glucose oxidase sensor and the pilocarpine iontophoresis method can be used to measure electrolytes in sweat alone or in conjunction with microfluidics system. Besides the support structures of the present invention, it is also understood that other articles such as watches, clothing, footwear and the like can be adapted to measure concentration of substances such as electrolytes present in sweat, however there is reduced clinical relevance for evaluating metabolic state of an individual outside the central nervous system.
Body abnormalities may cause a change in the pH, osmolarity, and temperature of the sweat derived from brain and neck blood vessels as well as change in the concentration of substances such as acid-lactic, glucose, lipids, hormones, gases, markers, infectious agents, antigens, antibody, enzymes, electrolytes such as sodium, potassium and chloride, and the like. Eyeglasses and any head gear can be adapted to measure the concentration of substances in sweat. Microminiature glass electrodes mounted in the end portion of the temple of eyeglasses sitting behind the ear or alternatively mounted on the lens rim against the forehead can be used to detect divalent cations such as calcium, as well as sodium and potassium ion and pH. Chloride-ion detectors can be used to detect the salt concentration in the sweat and the surface of the skin.
Many agents including biological warfare agents and HIV virus are present in sweat and could be detected with the eyeglasses or support structure on the head or face using sensors coated with antibodies against the agent which can create a photochemical reaction with appearance of colorimetric reaction and/or potential shift with subsequent change in voltage or temperature that can be detected and transmitted to a monitoring station or reported locally by audio or visual means. Electrocatalytic antibodies also can generate an electrical signal when there is an antigen-antibody interaction. It is also understood that other articles such as watches, clothing, footwear, and the like or any article capturing sweat can be adapted to identify antigens, antibody, infectious agents, markers (cancer, heart, genetic, metabolic, drugs, and the like) in accordance with the present invention. However, identification of those elements away from the central nervous system is of reduced clinical relevance.
The different amounts of fluid encountered in sweat can be easily quantified and the concentration of substances calibrated according to the amount of fluid in sweat. The relationship between the concentration of chemical substances and molecules in the blood and the amount of said chemical substances in the sweat can be described mathematically and programmed in a computer.
The present invention also includes eyeglasses or support structures in which a radio frequency transensor capable of measuring the negative resistance of nerve fibers is mounted in the eyeglasses or support structure. By measuring the electrical resistance, the effects of microorganisms, drugs, and poisons can be detected. The system also comprises eyeglasses in which a microminiature radiation-sensitive transensor is mounted in said eyeglasses or support structure.
The brain has a rich vasculature and receives about 15% of the resting cardiac output and due to the absence of fat the tunnel offers an area for optimal signal acquisition for evaluating hemodynamics. Accordingly, change in the viscosity of blood can be evaluated from a change in damping on a vibrating quartz micro-crystal mounted in the eyeglasses or support structure and the invention can be adapted to measure blood pressure and to provide instantaneous and continuous monitoring of blood pressure through an intact wall of a blood vessel from the brain and to evaluate hemodynamics and hydrodynamics. Also, by providing a contact microphone, arterial pressure can be measured using sonic devices.
Pressure can be applied to a blood vessel through a micro cuff mounted in the medial canthal pads, or alternatively by the temples of eyeglasses. Pressure can also be applied by a rigid structure, and the preferred end point is reached when sound related to blood turbulence is generated. The characteristic sound of systole (contraction of the heart) and diastole (relaxation of the heart) can be captured by the microphone. A microphone integrated into the medial canthal pad can be adapted to identify the heart sounds. Pressure transducers such as a capacitive pressure transducer with integral electronics for signal processing and a microphone can be incorporated in the same silicon structure and can be mounted in the medial canthal pad. Motion sensors and/or pressure sensors can be mounted in the medial canthal pad to measure pulse.
Reversible mechanical expansion methods, photometric, or electrochemical methods and electrodes can be mounted in the eyeglasses or support structures of the present invention and used to detect acidity, gases, analyte concentration, and the like. Oxygen gas can also be evaluated according to its magnetic properties or be analyzed by micro-polarographic sensors mounted in the eyeglasses or other support structure. A microminiature microphone mounted in the eyeglasses or other support structure can also be adapted to detect sounds from the heart, respiration, flow, vocal and the environment, which can be sensed and transmitted to a remote receiver or reported by local audio and visual means. The sensors are adapted and positioned to monitor the biological parameters at the end of the tunnel.
The eyeglasses or other support structures can also have elements which produce and radiate recognizable signals and this procedure could be used to locate and track individuals, particularly in military operations. A permanent magnet can also be mounted in the eyeglasses and used for tracking as described above. A fixed frequency transmitter can be mounted in the eyeglasses and used as a tracking device which utilizes a satellite tracking system by noting the frequency received from the fixed frequency transmitter to a passing satellite, or via Global Positioning Systems. Motion and deceleration can be detected by mounting an accelerometer in the eyeglasses. The use of eyeglasses as tracking devices can be useful for locating a kidnapped individual or for rescue operations in the military, since eyeglasses are normally unsuspecting articles.
The use of integrated circuits and advances occurring in transducer, power source, and signal processing technology allow for extreme miniaturization of the components which permits several sensors to be mounted in one unit.
The present invention provides continuous automated brain temperature monitoring without the need for a nurse. The present invention can identify a spike in temperature. Thus, proper diagnosis is made and therapy started in a timely fashion. Time is critical for identifying the temperature spike and organism causing the infection. Delay in identifying spike and starting therapy for the infection can lead to demise of the patient. The invention timely and automatically identifies the temperature spike and prevents the occurrence of complications.
The present invention also alerts the user about overheating or hypothermia to allow: 1. Proper hydration; 2. Increased performance; 3. Increased safety; and 4. Feed back control in treadmills and other exercise machines for keeping proper hydration and performance.
Annually many athletes, construction workers, college students and the general public unnecessarily die due to heatstrokes. Once the brain reaches a certain temperature level such as 40.degree. C., an almost irreversible process ensues. Because there are no specific symptoms and after a certain point there is rapid increase in brain temperature, heatstroke has one of the highest fatality rates. The more severe and more prolonged the episode, the worse the predicted outcome, especially when cooling is delayed. Without measuring core temperature and having an alert system when the temperature falls outside safe levels it is impossible to prevent hyperthermia and heatstroke. The present invention provides a device for continuous monitoring of temperature with alert systems that can prevent dangerous levels to be reached and cooling measures applied if needed. The apparatus can be adapted to be used in an unobtrusive manner by athletes, military, workers and the general population.
All chemical reactions in the body are dependent on temperature. High temperature can lead to enzymatic changes and protein denaturation and low temperature can slow down vital chemical reactions. Hydration is dependent on brain temperature and loss of fluid leads to a rise in brain temperature. Minimal fluctuations in the body's temperature can adversely affect performance and increase risk of illness and of life threatening events. Therefore, it is essential that athletes, sports participants, military personnel, police officers, firefighters, forest rangers, factory workers, farmers, construction workers and other professionals have precise mechanisms to know exactly what is their brain temperature.
When the core temperature rises, the blood that would otherwise be available for the muscles is used for cooling via respiration and perspiration. The body will do this automatically as temperature moves out of the preferred narrow range. It is this blood shifting that ultimately impairs physical performance and thermal induced damage to brain tissue interferes with normal cognitive function. Intense exercise can increase heat production in muscles 20 fold. In order to prevent hyperthermia and death by heat stroke athletes drink water. Because the ingestion of water is done in a random fashion, many times there is water intoxication which can lead to death as occurs to many healthy people including marathon runners and military personnel. Both, excess of water (overhydration) or lack of water (dehydration) can lead to fatal events besides reducing performance. Therefore, it is essential that individuals have precise means to know exactly when and how much to drink. By monitoring brain temperature with the present invention proper hydration can be achieved and athletes and military will know precisely when and how much water to ingest.
Timely ingestion of fluids according to the core temperature allows optimization of cardiovascular function and avoidance of heat strain. Because there is a delay from the time of ingestion of fluid to absorption of said fluid by the body, the method of invention includes signaling the need for ingestion at a lower core temperature such as 38.5.degree. C. to account for that delay, and thus avoid the onset of exhaustion. The temperature threshold can be adjusted according to each individual, the physical activity, and the ambient temperature.
In addition, software can be produced based on data acquired at the BTT site for optimizing fitness, athletic performance, and safety. The upper temperature limit of a particular athlete for maintaining optimal performance can be identified, and the data used to create software to guide said athlete during a competition. For instance, the athlete can be informed on the need to drink cold fluid to prevent reaching a certain temperature level which was identified as reduced performance for said athlete. Brain temperature level for optimal performance identified can be used to guide the effort of an athlete during competition and training. Hyperthermia also affects mental performance and software based on data from the BTT can be produced to optimize mental and physical performance of firefighters in an individual manner. People can have different thresholds for deleterious effects of hyperthermia and thus setting one level for all users may lead to underutilization of one's capabilities and putting others at risk of reduced performance. Likewise, exercise endurance and mental performance is markedly reduced by hypothermia and the same settings can be applied for low temperature situations. Determinations of brain temperature, oxygen and lactic acid levels can also be used for endurance training of athletes, fitness training, and to monitor the effects of training. The system, method, and apparatus of the invention provides a mechanism for enhancing safety and optimizing fitness for athletes and recreational sports participants.
It is a feature of the invention to provide a method for the precise and timely intake of fluids including the steps of measuring brain temperature, reporting the signal measured, and ingesting an amount of fluid based on the signal measured. Other steps can be included such as reporting devices using voice reproduction or visual devices to instruct on what beverage to drink and how much to drink to reduce core temperature. It is understood that the method of the present invention can combine measurement of temperature associated with measurement of sodium in sweat or blood, in accordance with the principles of the invention.
Children do not tolerate heat as well as adults because their bodies generate more heat relative to their size than adults do. Children are also not as quick to adjust to changes in temperatures. In addition, children have more skin surface relative to their body size which means they lose more water through evaporation from the skin. It is understood that different sizes, shapes, and designs of medial canthal pads including children size can be used in the present invention. Children eyeglasses equipped with sensors can have a booster radio transmitter that will transmit the signal to a remote receiver and alert parents about dangerous temperature levels. The eyeglasses can be incorporated with a detecting system to send a signal if the eyeglasses were removed or if the temperature sensor is not capturing signals in a proper manner. By way of illustration, but not of limitation, pressure sensing devices can be incorporated in the end of the temples to detect if the sunglasses are being worn, and an abrupt drop in the pressure signal indicates glasses were removed or misplacement of the sensor can also generate an identifiable signal. An adhesive, a double-sided adhesive tape, or other devices for increasing grip can be used in the medial canthal pads to ensure more stable position. It is understood that the eyeglasses can come equipped with sensors to detect ambient temperature and humidity, which allows for precisely alerting the wearer about any aspect affecting heat conditions.
In the current industrial, nuclear and military settings, personnel may be required to wear protective clothing. Although the protective clothing prevent harm by hazardous agents, the garments increase the rate of heat storage. It is understood that the present invention can be coupled with garments with adjustable permeability to automatically keep the core temperature within safe limits.
In addition, the present invention alerts an individual about risk of thermal damage (risk of wrinkles and cancer) at the beach or during outdoor activities. When one is at the beach, watching a game in a stadium, camping or being exposed to the sun, the radiant energy of the sun is absorbed and transformed into thermal energy. The combination of the different ways of heat transfer to the body lead to an increase in body temperature, which is reflected by the brain temperature. Convection and conduction can also lead to an increase in body temperature through heat transfer in the absence of sun light. The absorption of heat from the environment leads to a rise in the average kinetic energy of the molecules with subsequent increase in core temperature.
The levels of core temperature is related to the risk of thermal damage to the skin. After certain levels of heat there is an increased risk of denaturing protein and breaking of collagen in the skin. This can be compared with changes that occur when frying an egg. After a certain amount of thermal radiation is delivered the egg white changes from fluidic and transparent to a hard and white structure. After the egg white reaches a certain level of temperature the structural change becomes permanent. After a certain level of increase in core temperature during sun exposure, such as a level of 37.7.degree. Celsius to 37.9.degree. Celsius at rest (e.g.; sun bathing), thermal damage may ensue and due to the disruption of proteins and collagen there is an increased risk for wrinkle formation. The increased brain temperature correlates to the amount of thermal radiation absorbed by the body, and the duration of exposure of the temperature level times the level of temperature is an indicator of the risk of thermal damage, wrinkle formation, and skin cancer.
The present invention provides an alarm system that can be set up to alert in real time when it is time to avoid sun exposure in order to prevent further absorption of thermal radiation and reduce the risk of dermatologic changes, as can occur during outdoor activities or at the beach. In addition, thermal damage to the skin prevents the skin from adequately cooling itself and can result in increasing the risk of dehydration which further increases the temperature. The present invention helps preserve the beauty and health of people exposed to sun light and during outdoor activities while allowing full enjoyment of the sun and the benefits of sun light.
By the present invention, a method for timing sun exposure includes the steps of measuring body temperature, reporting the value measured and avoiding sun exposure for a certain period of time based on the level measured.
Hypothermia is the number one killer in outdoor activities in the U.S. and Europe. Hypothermia also decreases athletic performance and leads to injuries. It is very difficult to detect hypothermia because the symptoms are completely vague such as loss of orientation and clumsiness which are indistinguishable from general behavior. Without measuring core temperature and having an alert system when the temperature falls outside safe levels it is impossible to prevent hypothermia due to the vague symptoms. The present invention can alert an individual about hypothermia during skiing, scuba diving, mountain climbing and hiking. The present invention provides means to precisely inform when certain temperature thresholds are met, either too high or too low temperature.
The present invention continuously monitors the brain temperature and as soon as a temperature spike or fever occurs it activates diagnostics systems to detect the presence of infectious agents, which can be done locally in the BTT site, or the infectious agents can be identified in other parts of the body such as the blood stream or the eyelid pocket. The present invention can be also coupled to drug dispensing devices for the automated delivery of medications in accordance with the signal produced at the BTT site including transcutaneous devices, iontophoresis or by injection using a pump.
The invention also includes a tool for family planning. The system can detect spike and changes in basal temperature and identify moment of ovulation and phases of the menstrual cycle. This allows a woman to plan pregnancy or avoid pregnancy. This eliminates the need for invasive devices used for monitoring time for artificial insemination not only for humans but also animals. The invention can yet detect the start of uterine contractions (parturition) and allow a safer birth for animals. Support structures can be equally used in the BTT of animals.
The present invention also includes Automated Climate control according to the value measured at the BTT. The temperature of the user controls the temperature in a car. When the body starts to warm up, the signal from the apparatus of the invention automatically activates the air conditioner according to the user settings, alternatively it activates heat when the body is cold. This automation allows drivers to concentrate on the road and thus can reduce the risk for car crashes. It is understood that other articles that can affect body temperature can be controlled by the present invention including vehicle seats.
Current vehicle climate control systems are dramatically overpowered because they are designed to heat/cool the vehicle cabin air mass from an extreme initial temperature to a standard temperature within a certain period of time. Because people have different thermal needs for comfort, there is a consistent manual change of the temperature settings and said manual further increase consumption of energy. For instance, car temperature is set to remain at 73 F. Some people after 15 minutes may feel that it is too cold and some people may feel it is too hot. Subsequently the passenger changes the setting to 77 and then feels hot after another 10 minutes, and needs to manually change the set points again, and the process goes on. In addition the needs differ for people of different age, people with diabetes and other diseases, and male and female.
Manual frequent adjusting of a vehicle's climate control may increase fuel consumption 20% and increase emissions of pollutants such as carbon monoxide and nitrogen oxides.
The present invention provides an automated climate control in which the brain temperature controls the air conditioner and vehicle seats which maximizes comfort and minimizes fuel consumption. The improved fuel economy provided by the present invention protects the environment due to less pollutants affecting the ozone layer; improves public health by decreasing emission of toxic fumes, and increases driver's comfort and safety by less distractions with manually controlling a car's climate control.
Thermal environment inside transportation vehicles can be adjusted according to the temperature at the BTT site including contact sensor measurement and non-contact sensor measurement such as an infrared sensor or thermal image. The temperature at the BTT adjusts any article or device in the car that changes the temperature inside the cabin including air conditioner and heater, vehicle seats, doors, windows, steering wheels, carpets on the floor of the vehicle, and the like. Exemplarily, the temperature at the BTT site adjusts the amount of thermal radiation going through a window of a vehicle, if the BTT sends a signal indicating hot sensation then the windows for instance will darken to prevent further heat from entering the car, and vice versa if cold is perceived the window changing its light transmissibility to allow more heat waves to penetrate the vehicle's cabin. Any article touching the body or in the vicinity of the body can be adapted to change its temperature to achieve thermal comfort for the occupants of the vehicle.
Besides the support structures and thermal imaging systems described in the present invention to monitor and adjust temperature of a cabin of a transportation vehicle, it is understood that a contact lens inside the eyelid pocket with a temperature sensor can also be adapted to adjust the temperature inside the cabin of the vehicle. Exemplary transportation vehicles include cars, trucks, trains, airplanes, ships, boats, and the like.
It is also understood that the sensing system can include sensors in other parts of the body working in conjunction with the temperature sensor measuring temperature and/or thermal radiation at the BTT site. Thermal energy transfer from an article to an occupant of a vehicle can occur by any of radiation, convection, and the like, and any mechanism to transfer deliver, or remove thermal energy can be adjusted based on a temperature signal measured at the BTT.
The present invention provides a more energy-efficient system to achieve thermal comfort of the passengers in any type of transportation vehicle in existence or being developed with any type of sensor alone at the BTT site or in conjunction with sensors in other parts of the body.
Likewise, automated climate control at home, work, or any confined area can be achieved by activating the thermostat directly or via BlueTooth technology based on the temperature measured at the BTT in accordance with the present invention. Besides convenience and comfort, this automation allows saving energy since gross changes manually done in the thermostat leads to great energy expenditure.
It is understood that any body temperature measuring system can provide automated climate control or adjust temperature of articles in accordance with the principles of the present invention.
The present invention yet includes methods for reducing weight. It includes monitoring of temperature during programs for weight reduction based on increasing body heat to reduce said weight. The system alerts athletes on a weight losing program to prevent injury or death by overheating. The system can monitor temperature of people in sauna, steam rooms, spas and the like as part of weight reduction programs in order to prevent injuries and enhance results.
Yet, methods to enhance memory and performance besides preserving health is achieved by providing an automated mechanism to control ambient temperature and surrounding body temperature based on the brain temperature measured by the present invention. Human beings spend about one third of their lives sleeping. Many changes in body temperature occur during sleep. All of the metabolism and enzymatic reactions in the body are dependent on adequate level of temperature. The adequate control of ambient temperature which matches the needs of body temperature such as during sleeping have a key effect on metabolism. Adequate ambient temperature and surrounding temperature of objects which matches body temperature allow not only for people to sleep better, but also to achieve improved efficiency of enzymatic reactions which leads to improved mental ability and improved immune response. A variety of devices such as blankets, clothing, hats, mattress, pillows, or any article touching the body or in the vicinity of the body can be adapted to automatically increase or decrease temperature of said articles according to the temperature signal from the present invention.
The body naturally becomes cooler during the night and many people have restless sleep and turn continuously in bed because of that temperature effect. Since the tossing and turning occurs as involuntary movements and the person is not awake, said person cannot change the stimuli such as for instance increasing room temperature or increasing temperature of an electric blanket. The present invention automatically changes the ambient temperature or temperature of articles to match the temperature needs of the person. This is particularly useful for infants, elderly, diabetics, neuro-disorders, heart disease, and a variety of other conditions, since this population has reduced neurogenic response to changes in body temperature, and said population could suffer more during the night, have increased risk of complications besides decreased productivity due to sleep deprivation. Accordingly, the temperature of an electrical blanket or the ambient temperature is adjusted automatically in accordance with the temperature at the BTT. When low temperature at the BTT is detected by the apparatus of the invention a wireless or wired signal is transmitted to the article to increase its temperature, and in the case of an electrical blanket or heating system, the thermostat is automatically adjusted to deliver more heat.
The invention also provides devices and methods to be used with bio feedback activities. A brain temperature signal from the sensor at the BTT site produces a feedback signal as an audio tone or visual display indicating temperature and a series of tones or colors identify if the brain temperature is increasing (faster frequency and red) or decreasing (lower frequency and blue). The display devices can be connected by wires to the support structure holding the sensor at the BTT site.
Head cooling does not change brain temperature. Athletes, military, firefighters, construction workers and others are at risk of heatstroke despite pouring cold water on their head or using a fan. Medically speaking that is a dangerous situation because the cool feeling sensed in the head is interpreted as internal cooling and the physical activity is maintained, when in reality the brain remains at risk of thermal induced damage and heatstroke. Other medical challenges related to temperature disturbances concern response time. The brain has a slower recovery response to temperature changes than core temperature (internal temperature measured in rectum, bladder, esophagus, and other internal mechanisms). Thus, internal measurement may indicate stable temperature while the brain temperature remains outside safe levels, with risk of induced damage to cerebral tissue, either due to hypothermia or hyperthermia. The only medically acceptable way to prevent cerebral tissue damage due to temperature disturbances is by continuous monitoring brain temperature as provided by the present invention.
The present invention utilizes a plurality of active or passive sensors incorporated in support structures for accessing a physiologic tunnel for measuring biological parameters. The present invention preferably includes all functions in a miniature semiconductor chip, which as an integrated circuit, incorporates sensor, processing and transmitting units and control circuits.
Additional embodiments include temperature measurement and mass screening for fever and temperature disturbances (hyperthermia and hypothermia) comprising a body radiation detector, herein referred as a BTT ThermoScan, which comprises a thermal imaging system acquiring a thermal image of the end of the BTT. The BTT ThermoScan of the present invention has sufficient temperature and isotherm discrimination for monitoring temperature at all times and without the possibility of the measurement to be manipulated by artificial influences.
The BTT ThermoScan detects the brain temperature and provides an image corresponding to the BTT area or an image that includes the BTT area.
The BTT ThermoScan comprises a camera that converts thermal radiation into a video image that can be displayed on a screen, such as the images seen in
Human skin at the BTT site has a high emissivity (e in the Stefan-Boltzman formula) in the infrared range, nearly equal to a black body. A video image of people walking by and looking at the BTT ThermoScan lens is captured and a customized software is adapted to display a colored plot of isotherm lines, as the software used to acquire the image of
As shown in
In addition to cold challenges, hot challenges was performed in order to artificially increase body temperature and included exercise, people with sunburn, facing a heater, alcohol ingestion, cigarette smoking and body immersion in hot water. In all of those experiments the BTT area remained stable, but the remaining of the face had a change of temperature reflecting skin temperature, not internal brain temperature. As seen in
Many useful applications can be achieved including mass screening for fever, screening for hyperthermia in athletes at the end of a sports event (e.g., marathon), screening for hypothermia or hyperthermia for military personnel so as to select the one best fit physiologically for battle, and any other temperature disturbance in any condition in which a BTT ThermoScan can be installed.
One particular application consists of prevention of a terrorist attack by a terrorist getting infected with a disease (e.g., SARS—-Severe Acute Respiratory Syndrome) and deceiving thermometers to avert detection of fever when entering the country target for the terrorist attack.
SARS could potentially become a high terrorist threat because it cannot be destroyed. By being naturally created, SARS could become a weapon of mass destruction that cannot be eliminated despite use of military force or diplomatic means. A terrorist can get the infection with the purpose of spreading the infection in the target country. With current technology any device can be deceived and current devices would measure normal temperature when indeed fever is present. Simple means can be used by a terrorist, such as washing their face with cold water or ice or by immersion in cold water, to manipulate any device in the prior art used for measuring fever including current infrared imaging systems and thermometers. The thermal physiology of the body, as it is measured and evaluated by the prior art, can be manipulated and the measurement performed can give a false negative for fever.
A terrorist with SARS could easily spread the disease by many ways including individually by shaking hands with clerks on a daily basis on a mass scale by spending time in confined environments such as movie theater, a concert, grocery store, a government building, and others, or by contaminating water or drinking fountains. All of those people infected do not know they caught the disease and start to spread SARS to family members, co-workers, friends and others, who subsequently will infect others, leading to an epidemic situation.
From a medical standpoint, intentional spread of SARS can have immeasurable devastating effects. People not knowing they have the disease may go to a hospital for routine checks or people not feeling good may go to a hospital for routine checks. Patients and others coming to the hospital can then acquire the disease. Admitted patients, who are debilitated, can easily acquire SARS. Spread of SARS in a hospital environment can be devastating and the hospital may need to shut down. Therefore, one person with SARS can lead to the shut down of a whole hospital. Considering that people infected with the disease may go to different hospitals, several hospitals could get contaminated and would have to be partially or completely shut down. This could choke the health care system of a whole area, and patients would have to be transported to other hospitals. Those patients may have acquired SARS as well as perpetuating the transmission cycle. If this is done in several areas by a concerted terrorist effort, much of the health care system of a country could be choked, besides countless doctors and nurses could become infected with SARS which would further cripple the health care system by shortage of personnel.
The key to prevent the catastrophic effects of a terrorist attack is preparedness. The apparatus and methods of the present invention can detect SARS and cannot be manipulated by artificial means. Placement of the BTT ThermoScan of the present invention at the borders, ports and airports of a country can prevent the artificial manipulation of the temperature measurement and a possible terrorist attack. The system of the present invention can identify at all times and under any circumstances the presence of SARS and other diseases associated with fever.
In addition, mass screening of athletes could be performed with a BTT ThermoScan installed at the finish line. An alert is activated for any athlete who crosses the finish line with a high level of hyperthermia. Therefore immediate care can be delivered allowing for the best clinical outcome since any delay in identifying hyperthermia could lead to heatstroke and even death. The BTT ThermoScan is adapted to view at least a portion of the BTT area. BTT ThermoScan detects the brain temperature and provides an image corresponding to or that includes the BTT area. Despite athletes pouring water on their head, the BTT ThermoScan precisely detects the thermal status of the body by detecting the temperature at the BTT.
Temperature disturbances such as hyperthermia and hypothermia can impair mental and physical function of any worker. Drivers and pilots in particular can have reduced performance and risk of accidents when affected by temperature disturbances. The BTT ThermoScan can be mounted in the visor of a vehicle or plane to monitor body temperature with the camera of the BTT ThermoScan capturing a thermal image of the BTT of the driver or pilot and providing an alert whenever a disturbance is noticed. It is understood that any thermal imaging system can be mounted in a vehicle or airplane to monitor body temperature and alert drivers and pilots.
The BTT ThermoScan also includes monitoring mass screening of children and people at risk during flu season. With the shortage of nurses an automated screening can greatly enhance the delivery of health care to the ones in need. When a student walking by the infrared camera is identified as having a temperature disturbance (e.g., fever) a conventional digital camera is activated and takes a picture of the student. The picture can be emailed to the school nurse that can identify the student in need of care or automatically by using stored digital pictures.
Hospitals, factories, homes, or any location that can benefit from automated mass or individual screening of temperature disturbances can use the thermal imaging apparatus in accordance with the present invention.
It is understood that an apparatus comprised of a radiation source emitting a wavelength around 556 nm at the BTT site can be used for determining the concentration of hemoglobin. The hemoglobin present in the red blood cells at the terminal end of the BTT strongly absorbs the 556 nm wavelength and the reflected radiation acquired by a photodetector determines the amount of hemoglobin. Blood flow can be evaluated by knowing the amount with thermal radiation, the higher amount of the thermal radiation indicating higher blood flow in accordance to a mathematical model.
Positioning of contact sensors, non-contact sensors, and thermal imaging camera are facilitated by external visible anatomic aspects that may be present. The cerebral venous blood can be seen under the skin in the medial canthal area next to the corner of the eye. Therefore a method for measuring temperature includes the step of visually detecting the blue or bluish color of the skin at the BTT area and positioning the sensor on or adjacent to the blue or bluish area. For subjects of darker skin, a distinctive feature of difference skin texture in the BTT area next to the medial corner of the eye can be used as the reference for measurement.
The present invention includes devices for collecting thermal radiation from a BTT site, devices for positioning temperature sensitive devices to receive thermal radiation from the BTT site and devices for converting said thermal radiation into the brain temperature. The present invention also provides methods for determining brain temperature with said methods including the steps of collecting the thermal emission from the BTT site, producing a signal corresponding to the thermal emission collected, processing the signal and reporting the temperature level. The invention also includes devices and methods for proper positioning of the temperature sensor in a stable position at the BTT site.
It is also an object of the present invention to provide support structures adapted to position a sensor on the end of a tunnel on the skin to measure biological parameters.
It is an object of the present invention to provide apparatus and methods to measure brain temperature including patches, adhesives strips, elastic devices, clips and the like containing sensors positioned on a physiologic tunnel.
It is an object of the present invention to provide apparatus and methods to measure brain temperature including thermal imaging systems containing infrared sensors sensing infrared radiation from the BTT.
It is an object of the present invention to provide multipurpose eyeglasses equipped with medial canthal pads containing sensors positioned on a physiologic tunnel for measuring biological parameters
It is another object of the present invention to provide new methods and apparatus for measuring at least one of brain temperature, chemical function and physical function.
It is yet an object of the invention to provide apparatus that fit on both adults and children.
It is also an object of the invention to provide apparatus that report the signal produced at the tunnel by at least one of wired connection to reporting devices, wireless transmission to reporting devices and local reporting by audio, visual or tactile devices such as by vibration incorporated in support structures.
It is yet another object of the present invention to provide apparatus that allow the wearer to avoid dehydration or overhydration (water intoxication).
It is a further object of the present invention to provide methods and apparatus that allows athletes and sports participants to increase their performance and safety.
It is yet an object of the present invention to provide support structure positioned sensors on a tunnel which can be worn at least by one of athletes during practice and competition, military during training and combat, workers during labor and the general public during regular activities.
It is another object of the present invention to increase safety and comfort in vehicles by providing automated climate control and vehicle seat control based on the core temperature of the occupants of the vehicle.
It is an object of the present invention to provide methods and apparatus that act on a second device based on the level of the biological parameter measured.
It is another object of the invention to provide methods and apparatus to preserve skin health, reduce risk of wrinkles and reduce the risk of skin cancer by preventing sun damage by thermal radiation and alerting the wearer when the temperature has reached certain thresholds.
It is also an object of the invention to provide methods and apparatus for achieving controlled weight loss based on heat-based weight loss approach.
It is also an object of the invention to provide methods and apparatus to alert athletes in a weight losing program based on increasing body temperature to prevent injury or death by overheating.
It is also an object of the invention to provide methods and apparatus that allow monitoring fever and spikes of temperature.
It is also an object of the invention to provide a device for family planning by detecting time of ovulation.
It is a further object of the invention to provide methods and apparatus for the delivery of medications in accordance with the signal produced at the tunnel.
It is yet an object of the invention to provide methods and apparatus that enhance occupational safety by continually monitoring biological parameters.
It is also an object of the invention to provide an article of manufacture with a sensing apparatus positioned on a tunnel for monitoring biological parameters that can be fitted or mounted in at least one of the frame of eyeglasses, the nose pads of eyeglasses, the structure of a head mounted gear and clothing.
The invention also features transmitting the signal from the support structure to act on at least one of exercise equipment, bikes, sports gear, protective clothing, footwear and medical devices.
It is yet an object of the invention to provide support structures that transmit the signal produced at the tunnel to treadmills and other exercise machines for keeping proper hydration and preventing temperature disturbances of the user.
It is yet another object of the invention to provide apparatus and methods for monitoring biological parameters by accessing a physiologic tunnel using active or passive devices.
The invention yet features transmission of the signal from the support structures to watches, pagers, cell phones, computers, and the like.
This disclosure provides a system for cooling a human, comprising a temperature sensor, a cooling apparatus, at least one of an alarm and a display, and a controller. The temperature sensor is configured to transmit a signal representative of temperature positioned on skin of the human on, over, or adjacent the brain thermal tunnel terminus. The cooling apparatus is positioned to provide cooling to the human. The controller is configured to receive the temperature signal, to determine from the temperature signal a first temperature representative of an uncooled condition of the human, to determine when the temperature signal is indicative of a second temperature that is at least one degree Celsius less than the first temperature, and to transmit a signal to at least one of the alarm and the display to present an indication that the second temperature has been reached.
This disclosure also provides a system for modifying a core temperature for a human, comprising a temperature sensor, a temperature modifying apparatus, at least one of an alarm and a display, and a controller. The temperature sensor is positioned and configured to transmit a signal representative of temperature of skin of the human on, over, or adjacent the brain thermal tunnel terminus. The temperature modifying apparatus is positioned to provide temperature modification for the human. The controller is configured to receive the temperature signal, to determine from the temperature signal a first temperature representative of a baseline condition of the human, to determine when the temperature signal is indicative of a second temperature that is at least 0.5 degrees Celsius different from the first temperature, and to transmit a signal to at least one of the alarm and the display to present an indication that the second temperature has been reached.
This disclosure also provides a system for analyzing the brain thermal tunnel temperature of a human, the system comprising a temperature sensor and a controller. The temperature sensor is positioned and configured to transmit a signal representative of temperature positioned on skin of the human on, adjacent, or over the brain thermal tunnel. The controller is positioned to receive the temperature signal and configured to provide a frequency analysis of the temperature signal, the frequency analysis having a plurality of frequency peaks. The controller is configured to determine from an amplitude of each frequency peak a slope, and the controller is configured to determine when the slope exceeds a predetermined non-zero slope indicative of a medical condition in the human.
This disclosure also provides a system for analyzing the brain thermal tunnel temperature of a human, the system comprising a temperature sensor and a controller. The temperature sensor is positioned and configured to transmit a signal representative of temperature on skin of the human on, over, or adjacent the brain thermal tunnel terminus. The controller is positioned to receive the temperature signal and configured to provide a frequency analysis of the temperature signal, the frequency analysis having a plurality of frequency peaks. The controller is configured to determine when the average spacing of the plurality of frequency peaks in a predetermined frequency range exceeds a predetermined spacing indicative of a medical condition in the human.
This disclosure also provides a system for detecting a sleep condition of a human, comprising a temperature sensor and a controller. The temperature sensor is positioned and configured to transmit a signal representative of temperature on skin of the human on, over, or adjacent the brain thermal tunnel terminus. The controller is configured to receive the temperature signal, to determine from the temperature signal a temperature decline of at least 0.2° C. in a period of one minute, so as to identify a sleep condition when the temperature decline of 0.2° C. in a period of one minute occurs.
This disclosure also provides a method of detecting a sleep condition of a human, comprising measuring the temperature of skin of the human on, over, or adjacent the brain thermal tunnel terminus; and identifying a sleep condition by identifying a temperature decline of at least 0.2° C. in a period of one minute.
This disclosure also provides a temperature measuring apparatus, comprising a temperature sensor, at least one indicator having a variable output, and a controller. The temperature sensor is configured to measure temperature and to transmit a signal representing the measured temperature to a controller. The controller is configured to receive the temperature signal, to identify a peak temperature in a predetermined region of a human or animal subject, and to vary the indicator in proportion to the measured temperature in comparison to the peak temperature.
This disclosure also provides a temperature measuring apparatus, comprising a skin contact temperature sensor, a plurality of indictors, and a controller. The skin contact temperature sensor is configured to measure temperature and to transmit a signal representing the measured temperature to a controller. The controller is configured to receive the temperature signal, to identify a peak temperature in a predetermined region of a human or animal subject, and to vary the plurality of indicators to indicate a direction towards or away from the peak temperature.
Advantages and features of the embodiments of this disclosure will become more apparent from the following detailed description of exemplary embodiments when viewed in conjunction with the accompanying drawings.
These and other objects of the invention, as well as many of the intended advantages thereof, will become more readily apparent when reference is made to the following description taken in conjunction with the accompanying drawings.
FIGS. 19A1, 19A2, 19B, 19C and 19D are schematic diagrams of preferred geometry and dimensions of support structures and sensing devices.
FIG. 86M(1) illustrates a rear view of an adhesive patch.
FIG. 86P(1) diagrammatically illustrates the noncontact measurement of the brain tunnel.
FIG. 86P(2) schematically illustrates a light source directing radiation at the brain tunnel and measurement of reflected radiation.
FIG. 86P(3) diagrammatically illustrates a handheld sensing device for noncontact measurement at the brain tunnel.
FIG. 86P(4) illustrates a noncontact measurement at the brain tunnel.
FIG. 86P(5) illustrates a sensing device and a sensor mounted on a web-camera for measurement of radiation from the brain tunnel.
FIG. 86Q(1) is a perspective diagrammatic view of a measuring portion of a sensor assembly.
FIG. 86R(1) illustrates a sensing device worn by a user.
FIG. 86R(2) illustrates a sensing device having a swivel mechanism at the junction of an arm and a body.
FIG. 86R(3) illustrates the swivel assembly of a sensing device and support structure worn by a user.
FIG. 86S(1) is a side view of a sensing device having a straight extending wire.
FIG. 86S(2) shows a sensing device worn by a user with an arm bent into position.
FIG. 86T(1) illustrates a sensing device including an arm, measuring portion and plate.
FIG. 86T(2) shows a sensing device and support structure formed of separable pieces.
FIG. 86T(3) shows an alternate embodiment of a sensing device and support structure with different separable pieces from FIG. 86T(2).
FIG. 96-G1 illustrates a glucose sensing device.
FIG. 96-G2 illustrates a specialized cap of a sensing device.
In describing a preferred embodiment of the invention illustrated in the drawings, specific terminology will be resorted to for the sake of clarity. However, the invention is not intended to be limited to the specific terms so selected, and it is to be understood that each specific term includes all technical equivalents which operate in a similar manner to accomplish a similar purpose.
The scale indicates the range of temperature found in the human face. The hottest spots are indicated by the brightest white spots and the coldest areas are black. Temperature between the hottest and coldest areas are seen in different hues in a gray scale. The nose is cold (seen as black) since it is primarily composed of cartilage and bones, and consequently has a lower blood volume. That is the reason why frostbite is most common in the nose.
The surrounding periocular area of the upper and lower eyelids (seen as gray) is hotter because of high vascularization and the reduced amount of adipose tissue. The skin underneath the eyelids is very thin and does not have adipose tissue either. However, the other conditions necessary to define a brain temperature tunnel are not present in this area.
The BTT requirements also include the presence of a terminal branch to deliver the total amount of heat, a terminal branch that is a direct branch from a vessel from the brain, a terminal branch that is superficially located to avoid far-infrared radiation absorption by other structures, and no thermoregulatory arteriovenous shunts. Thus, the BTT, i.e., the skin area in the medial corner of the eye and upper eyelid, is the unique location that can access a brain temperature tunnel. The skin around the eyelids delivers undisturbed signals for chemical measurements using spectroscopy and is defined as a metabolic tunnel with optimal acquisition of signals for chemical evaluation, but not for evaluation of the total radiant power of the brain.
The main entry point is the area of most optimal signal acquisition. The image also shows the symmetry of thermal energy between the two BTT sites. Since other areas including the forehead do not have the aforementioned six characteristics needed to define a BTT, said areas have lower total radiant power seen as light and dark green. Thus the forehead is not suitable to measure total radiant power. The whole nose has very little radiant power seen as blue and purple areas, and the tip of the nose seen as brown has the lowest temperature of the face. Thus, the nose area is not suitable for measuring biological parameters.
The total radiated power (P) at the end of the tunnel is defined by P=.sigma.*e*A*T.sup.4, where .sigma. is the Stefan-Boltzman constant with a value .sigma.=5.67.times.10.sup.−8 Wm.sup.−2K.sup.−4 and e is the emissivity of the area. Since the end of the tunnel provides an optimal area for radiation, the total power radiated grows rapidly as the temperature of the brain increases because of the T.sup.4 term in the equation. As demonstrated in the experiments in the present invention mentioned, the radiated power in the BTT occurred at a faster rate than the radiated power in the tongue and oral cavity.
The BTT site on the skin is a very small area measuring only less than 0.5% of the body surface area. However, this very small skin region of the body provides the area for the optimal signal acquisition for measuring both physical and chemical parameters.
Thermal energy from the sinus cavernous in the brain 10 is transferred to the end of the tunnel 16 and a rapid rate of heat transfer occurs through the unimpeded cerebral venous blood path. The tunnel also has a wall 18 representing the wall of the vasculature storing the thermal energy with equivalent temperature and serving as a conduit from the inside of the body 10 to the exterior (skin surface) 19 which ends as a terminal vessel 17 transferring the total amount of thermal energy to said skin 19.
The skin 19 is very thin and allows high heat flow. The thickness of skin 19 is negligible compared to the skin 39, 49 in non-tunnel areas 30 and 40 respectively. Due to the characteristics of skin 19, high heat flow occurs and thermal equilibrium is achieved rapidly when a sensor is placed on the skin 19 at the end of the BTT 20.
In other areas of skin in the face and in the body in general, and in the exemplary non-tunnel areas 30 and 40 of
Contrary to that, the tunnel area 20 is homogeneous with no absorption of infrared energy and the blood vessels are located on the surface. This allows undisturbed delivery of infrared energy to the surface of the skin 19 and to a temperature detector such as an infrared detector placed in apposition to said skin 19. In the BTT area there is no thermal gradient since there is only a thin layer of skin 19 with terminal blood vessel 17 directly underneath said thin interface skin 19. The thermal energy 16 generated by the terminal blood vessel 17 exiting to the surface skin 19 corresponds to the undisturbed brain (true core) temperature of the body. The preferred path for achieving thermal equilibrium with brain tissue temperature is through the central venous system which exits the brain and enters the orbit as the superior ophthalmic vein. The arterial blood is 0.2 to 0.3 degrees Celsius lower when compared to the central venous blood, and said arterial blood is not the actual equivalent of the brain temperature. Thus although arterial blood may be of interest in certain occasions, the venous system is the preferred carrier of thermal energy for measurement of brain temperature. Arterial blood temperature may be of interest to determine possible brain cooling by the arterial blood in certain circumstances.
Non-tunnel areas 30 and 40 are characterized by the presence of heat absorbing elements. The non-tunnel areas 30 and 40 are defined by broken lines characterizing the vulnerability of interference by heat absorbing constituents and by the disorganized transferring of heat in said non-tunnel areas 30 and 40. Various layers and other constituents in non-tunnel areas 30 and 40 selectively absorb infrared energy emitted by the deeper layers before said energy reaches the surface of skin, and the different thermal energy and the different areas are represented by the different shapes and sizes of arrows and arrow heads.
Non-tunnel area 30 can be representative of measuring temperature with a sensor on top of the skin anatomically located above the heart 32. White arrows 34 represent the thermal energy in the heart 32. Non-tunnel area 30 includes the heart 32 and the various blood vessels and its branches 36a, 36b, 36c, 36d storing thermal energy.
Different amounts of heat are transferred and different temperatures measured depending on the location and anatomy of blood vessels 36a, 36b, 36c. The blood vessels branch out extensively from the main trunk 34a. The non-tunnel area 30 also includes heat absorbing structures 37 such as bone and muscles which thermal energy 34 from the heart 32 need to be traversed to reach the skin 39. The non-tunnel area 30 also includes a variable layer of fat tissue 38 which further absorbs thermal energy. The reduced amount of thermal energy reaching the skin surface due to the presence of fat 38 is represented by the arrows 36d and 36e, in which arrow 36d has higher temperature than arrow 36e. Non-tunnel area 30 also includes a thick skin 39 with low heat flow represented by arrows 36f.
The thick skin 39 corresponds to the skin in the chest area and fat layer 38 corresponds to the variable amount of fat present in the chest area. Arrows 36g represent the disordered and reduced total radiant power delivered after said thermal energy traverses the interfering constituents in the non-tunnel area including a thick interface and heat absorbing structures. In addition, BTT 20 has no fat layer as found in non-tunnel areas 30 and 40. Lack of a thick interface such as thick skin and fat, lack of thermal barriers such as fat, and lack of heat absorbing elements such as muscles allows undisturbed emission of radiation at the end of the BTT. Lack of a thick interface such as thick skin and fat, lack of thermal barriers such as fat, and lack of heat absorbing elements such as muscles allowed undisturbed emission of radiation at the end of the BTT.
Yet referring to
Measurements of internal temperature such as rectal do not have the same clinical relevance as measurement in the brain. Selective brain cooling has been demonstrated in a number of mammalian species under laboratory conditions and the same process could occur in humans. For instance the temperature in bladder and rectum may be quite different than the brain. High or low temperature in the brain may not be reflected in the temperature measured in other internal organs.
The heat generated by metabolic rate in the brain corresponds to 20% of the total heat produced by the body and this enormous amount of heat is kept in a confined and thermally sealed space. Brain tissue is the most susceptible tissue to thermal energy induced damage, both high and low levels of thermal energy. Because of the thermal insulation and physical inability of the brain to gain heat or lose heat, both hypothermic (cold) and hyperthermic (hot) states can lead to brain damage and death can rapidly ensue, as occur to thousands of healthy people annually besides seizures and death due to high fever in sick people. Unless appropriate and timely warning is provided by continuously monitoring brain temperature anyone affected by cold or hot disturbances is at risk of thermal induced damage to the brain.
The tunnel 20 starts at the cavernous sinus 1 which is a conduit for venous drainage for the brain and for heat transfer at the end of the tunnel 20 as a radiant energy. Tunnel 20 provides an unobstructed passage to the cavernous sinus 1, a structure located in the middle of the brain, and which is in direct contact with the two sources of heat to the brain: 1) thermal energy produced due to metabolic rate by the brain and carried by the venous system; and 2) thermal energy delivered by the arterial supply from the rest of the body to the brain. This direct contact arrangement is showed in detail in
As soon as cold blood reaches the cavernous sinus 1 the corresponding thermal energy state is transferred to the tunnel and to the skin surface at the end of the tunnel, providing therefore an immediate alert even before the cold blood is distributed throughout the brain. The same applies to hot blood for instance generated during exercise which can lead to a 20 fold heat production compared to baseline. This heat carried by vessels 8a, 8b is transferred to the cavernous sinus 1 and can be measured at the end of the tunnel. In addition, the thermal energy generated by the brain is carried by cerebral venous blood and the cavernous sinus 1 is a structure filled with venous blood.
The internal areas of the tunnel 50 include the general area for the main entry point and the main entry point as shown in
The main entry point is the preferred location for the positioning of the sensor by the support structure, but the placement of a sensor in any part of the end of the tunnel including the general entry point area and peripheral area provides clinically useful measurements depending on the application. The degree of precision needed for the measurement will determine the positioning of the sensor. In cases of neurosurgery, cardiovascular surgery, or other surgical procedures in which the patient is at high risk of hypothermia or malignant hyperthermia, the preferred position of the sensor is at the main entry point. For recreational or professional sports, military, workers, fever detection at home, wrinkle protection in sunlight, and the like, positioning the sensor in any part of the end of the tunnel area provides the precision needed for clinical usefulness.
In accordance with the present invention,
To determine the thermal stability of the tunnel area in relation to environmental changes, cold and heat challenge tests were performed.
A preferred embodiment includes a temperature sensor with measurement processing electronics housed in a patch-like support structure which positions a passive sensor directly in contact with the skin over the brain temperature tunnel site. Accordingly,
The antenna 78 can be secured to a mattress, pillow, frame of a bed, and the like in a removable or permanent manner. The preferred embodiment includes a thin flat antenna encapsulated by a flexible polymer that is secured to a mattress and is not visible to the user. Alternatively an antenna can be placed in any area surrounding the patient, such as on a night stand.
The antenna 78 and controller unit 84 works as a receiver/interrogator. A receiver/interrogator antenna 78 causes RF energy to radiate to the microcircuit in the patch 72. This energy would be stored and converted for use in the temperature measurement process and in the transmission of the data from the patch 72 to the antenna 78. Once sufficient energy has been transferred, the microcircuit makes the measurement and transmits that data to the receiver/interrogator antenna 78 with said data being processed at controller 84 and further communicated to device 88 for display or further transmission. The switching elements involved in the acquisition of the sensor data (measurement of the energy) is done in a sequence so that the quantitized answer is available and stored prior to the activation of the noise-rich transmission signal. Thus the two inherently incompatible processes successfully coexist because they are not active simultaneously.
The capability of the RF link to communicate in the presence of noise is accomplished by “spreading” the spectral content of the transmitted energy in a way that would inherently add redundancy to the transmission while reducing the probability that the transmission can ever be interpreted by the receiver/interrogator 78 as another transmission or noise that would cause the receiver/interrogator 78 to transmit and display incorrect information. This wireless transmission scheme can be implemented with very few active elements. The modulation purposely spreads the transmission energy across the spectrum and thus provides noise immunity and the system can be ultimately produced via batch processing and thus at a very low cost.
Since the energy to operate sensor 74 in patch 72 comes from the antenna 78, the microcircuit in said patch 72 can be very small and ultra-thin. Size of the patch 72 would be further minimized to extremely small dimensions by the design approach that places all the processing function of the RF link in the controller unit 84 working as a receiver. RF messaging protocol and the control of the sensor 74 resides in the receiver/interrogator controller powered by commercially available batteries or by AC current. Thus the RF messaging protocol and the control of the sensor 74 is directly controlled by the MCU of controller 84. The circuit resident in the patch 72 is preferably completely self-contained. The sensing system 74 in the patch 72 is preferably a silicon microcircuit containing the circuits needed to support the sensor, quantatize the data from the sensor, encode the data for radio frequency transmission, and transmit the data, besides power conditioning circuits and digital state control. Sensor, support circuitry, RF power and communications are all deposited on a micro-chip die allowing the circuit to be built in large quantities and at very low cost. This scheme is preferably used for both passive and active devices.
The operational process can consist of two modes, manual or automated. In the manual mode, an operator such as a nurse activates the system and RF energy radiated to the microcircuit in the patch 72 would be stored and converted for use in the temperature measurement process and in the transmission of the data from the end of the BTT to the antenna 78. Once sufficient energy has been transferred (less than 1 second) the microcircuit would make the measurement and transmit the data to the antenna 78 receiver and controller 84 to be displayed for example on a back-lit LCD display at the nursing station. An audio “beep” will signal that the data had been received and is ready for view. In the automated mode, the process is done automatically and continuously by interrogation at preset frequency and an alarm being activated when the reading is outside the specified range. A tri-dimensional antenna can also be used and the controller 84 set up to search the three dimensions of the antenna to assure continued and proper connection between antenna 78 and sensing means 74. It is also understood that the sensor can modulate reflected RF energy. Accordingly, the energy will trigger the unit to acquire a temperature measurement, and then the unit will modulate the reflected energy. This reflected energy and information will be received at the interrogator and displayed as above.
The present invention also provides a method for monitoring biological parameters, which comprises the steps of: securing a passive sensor to the body; generating electromagnetic radiation from a device secured to at least one of a mattress, a pillow and the frame of a bed; generating a signal from said passive sensor; receiving said signal by a device secured to at least one of a mattress, a pillow and the frame of a bed; and determining the value of the biological parameter based on said signal.
It is understood that a variety of external power sources such as electromagnetic coupling can be used including an ultra-capacitor charged externally through electromagnetic induction coupling and cells that can be recharged by an external oscillator. It is also understood that the sensing system can be remotely driven by ultrasonic waves.
The preferred embodiments shown in
In accordance with this exemplary embodiment for temperature measurement, the thermal energy emitted by the BTT is sensed by the temperature sensor 102 such as a miniature thermistor which produces a signal representing the thermal energy sensed. The signal is then converted to digital information and processed by processor 106 using standard processing for determining the temperature. An exemplary sonic-based system for brain temperature measurement comprises a temperature sensor, input coupling circuit, signal processing circuit, output coupling circuit and output display circuit. A temperature sensor 102 (e.g., thermistor) in a patch 109 placed on the surface of the skin at the medial canthal area responds to variations in brain temperature which is manifested as a DC voltage signal.
This signal, coupled to a Signal Processor Circuit via an Input Coupling Circuit is used to modulate the output of an oscillator, e.g., a multivibrator circuit, piezoelectric systems operating in or just above the audio frequency range. The oscillator is a primary component of the Signal Processor Circuit. The output of the oscillator is input to an amplifier, which is the second primary component of the Signal Processor.
The amplifier increases the output level from the oscillator so that the output of the Signal Processor is sufficient to drive an Output Display Circuit. Depending on the nature of the Output Display Circuit, e.g., an audio speaker, a visual LED display, or other possible display embodiment, an Output Coupling Circuit is utilized to match the signal from the Signal Processor Circuit to the Output Display Circuit. For an Output Display Circuit that requires a digital input signal, the Output Coupling Circuit might include an analog to digital (A/D) converter circuit. A DC power supply circuit is the remaining primary component in the Signal Processor Module. The DC power supply is required to support the operation of the oscillator and the amplifier in the Signal Processing Circuit. Embodiments of the DC power supply can include ultra miniature DC batteries, a light sensitive DC power source, or some combination of the two, and the like. The micro transducers, signal processing electronics, transmitters and power source can be preferably constructed as an Application Specific Integrated Circuit or as a hybrid circuit alone or in combination with MEMS (micro electrical mechanical systems) technology.
The thermistor voltage is input to a microcontroller unit, i.e., a single chip microprocessor, which is pre-programmed to process the thermistor voltage into a digital signal which corresponds to the patient's measured temperature in degrees C. (or degrees F.) at the BTT site. It is understood that different programming and schemes can be used. For example, the sensor voltage can be directly fed into the microcontroller for conversion to a temperature value and then displayed on a screen as a temperature value, e.g., 98.6.degree. F. On the other hand the voltage can be processed through an analog to digital converter (ADC) before it is input to the microcontroller.
The microcontroller output, after additional signal conditioning, serves as the driver for a piezoelectric audio frequency (ultrasonic) transmitter. The piezoelectric transmitter wirelessly sends digital pulses that can be recognized by software in a clock radio sized receiver module consisting of a microphone, low-pass audio filter, amplifier, microcontroller unit, local temperature display and pre-selected temperature level alert mechanism. The signal processing software is pre-programmed into the microcontroller unit of the receiver. Although the present invention provides means for RF transmission in the presence of noise, this particular embodiment using a microphone as the receiving unit may offer additional advantages in the hospital setting since there is zero RF interference with the many other RF devices usually present in said setting. The microcontroller unit drives a temperature display for each patient being monitored. Each transmitter is tagged with its own ID. Thus one receiver module can be used for various patients. A watch, cell phone, and the like adapted with a microphone can also work as the receiver module.
In another embodiment the output of the microcontroller is used to drive a piezo-electric buzzer. The microcontroller output drives the piezo-electric buzzer to alert the user of the health threatening situation. In this design the output of the microcontroller may be fed into a digital-to-analog converter (DAC) that transforms the digital data signal from the microcontroller to an equivalent analog signal which is used to drive the buzzer.
In yet another embodiment the output from the (DAC) is used to drive a speech synthesizer chip programmed to output an appropriate audio warning to the user, for instance an athlete at risk of heatstroke. For a sensed temperature above 39 degrees Celsius the message might be: “Your Body temperature is High. Seek shade. Drink cold liquid. Rest.” For temperature below 36 degrees Celsius the message might be: “Your Body temperature is Low. Seek shelter from the Cold. Drink warm liquid. Warm up.”
In another embodiment the output is used to drive a light transmitter programmed to output an appropriate light signal. The transmitter consists of an infrared light that is activated when the temperature reaches a certain level. The light signal will work as a remote control unit that activates a remote unit that sounds an alarm. This embodiment for instance can alert the parents during the night when the child is sleeping and has a temperature spike.
An exemplary embodiment of the platform for local reporting consists of three electronic modules mechanically housed in a fabric or plastic holder such as patch 109, which contain a sensor 102 positioned on the skin at the BTT site. The modules are: Temperature Sensor Module, Microcontroller Module, and Output Display Module in addition to a battery. An electronic interface is used between each module for the overall device to properly function. The configuration of this system consists of a strip such as patch 109 attached to the BTT area by a self-adhesive pad. A thermistor coupled to a microcontroller drives an audio frequency piezoelectric transmitter or LED. The system provides local reporting of temperature without a receiver. An audio tone or light will alert the user when certain thresholds are met. The tone can work as a chime or reproduction of human voice.
Another exemplary embodiment for remote reporting consists of four electronic modules: Sensor Module, Microcontroller Module, Output Transmitter Module and Receiver/Monitor Module. From a mechanical viewpoint the first three modules are virtually identical to the first embodiment. Electronically the Temperature Sensor and Microprocessor Modules are identical to the previous embodiment. In this embodiment an Output Transmitter Module replaces the previous local Output Display Module. Output Transmitter Module is designed to transmit wirelessly the temperature results determined by the Microprocessor Module to a remotely located Receiver/Monitor Module. An electronic interface is used between each module for proper function. This device can be utilized by patients in a hospital or home setting. On a continuous basis temperature levels can be obtained by accessing data provided by the Receiver/Monitor Module.
A variety of temperature sensing elements can be used as a temperature sensor including a thermistor, thermocouple, or RTD (Resistance Temperature Detector), platinum wire, surface mounted sensors, semiconductors, thermoelectric systems which measure surface temperature, optic fiber which fluoresces, bimetallic devices, liquid expansion devices, and change-of-state devices, heat flux sensor, crystal thermometry and reversible temperature indicators including liquid crystal Mylar sheets. A preferred temperature sensor includes thermistor model 104JT available from Shibaura of Japan.
Receiver 130 preferably includes a chip RF transceiver 132 (e.g., CC1000 available from Chipcon Corporation), a microcontroller unit (MCU) 134, amplifier and filtering units (A/F) 136, display 138, clock 140, keypad 142, LED 144, speaker 146, in addition to a power source 150 and input/output units (I/O) 148 and associated modem 152, optical transceiver 154 and communication ports 156.
A variety of devices can be used for the transmission scheme besides the commercially available RF transmitter chips previously mentioned. One simple transmission devices include an apparatus with a single channel transmitter in the 916.48 MHz band that sends the temperature readings to a bed side receiver as a frequency proportional to the reading. The thermistor's resistance would control the frequency of an oscillator feeding the RF transmitter data input. If the duty cycle is less than 1%, the 318 MHz band would be usable. Rather than frequency, a period measurement technique can be used. The model uses a simple radio frequency carrier as the information transport and modulating that carrier with the brain temperature information derived from a transduction device capable of changing its electrical characteristics as a function of temperature (e.g.; thermistor). Either frequency or amplitude of the carrier would be modulated by the temperature information so that a receiver tuned to that frequency could demodulate the changing carrier and recover the slowly moving temperature data.
Another transmission technique suitable to transmit the signal from a sensor in a support structure is a chirp device. This means that when activated, the transmitter outputs a carrier that starts at a lower frequency in the ISM band and smoothly increases frequency with time until a maximum frequency is reached. The brain temperature information is used to modify the rate of change of frequency of the chirp. The receiver is designed to measure the chirp input very accurately by looking for two or more specific frequencies. When the first of the frequencies is detected, a clock measures the elapsed time until the second frequency is received. Accordingly, a third, fourth, etc., frequency could be added to aid in the rejection of noise. Since virtually all the direct sequence spread spectrum transmitters and frequency hopping transmitters are spread randomly throughout their part of the ISM band, the probability of them actually producing the “right” sequence of frequencies at exactly the right time is remote.
Once the receiver measured the timing between the target frequencies, that time is the value that would represent the brain temperature. If the expected second, third, or fourth frequency is not received by the receiver within a “known” time window, the receiver rejects the initial inputs as noise. This provides a spread spectrum system by using a wide spectrum for transmitting the information while encoding the information in a way that is unlike the expected noise from other users of the ISM band. The chirp transmitter is low cost and simple to build and the brain temperature transducer is one of the active elements that controls the rate of change of frequency.
Other preferred embodiments for local reporting include a sensor, an operational amplifier (LM358 available from National Semiconductor Corporation) and a LED in addition to a power source. It is understood that the operational amplifier (Op Amp) can be substituted by a MCU and the LED substituted by a piezoelectric component.
The preferred embodiment allows precise positioning of the sensing apparatus by the support structure on the BTT site. The support structure is designed to conform to the anatomical landmarks of the BTT area which assures proper placement of the sensor at all times. The corner of the eye is considered a permanent anatomic landmark, i.e., it is present in the same location in all human beings. The BTT area is also a permanent anatomic landmark as demonstrated by the present invention. To facilitate consistent placement at the BTT site, an indicator in the support structure can be used as shown in
In
The material for the support structure working as a patch can be soft and have insulating properties such as are found in polyethylene. Depending on the application a multilayer structure of the patch can include from the external side to the skin side the following: thinsulate layer; double foam adhesive (polyethylene); sensor (thermistor); and a Mylar sheet. The sensor surface can be covered by the Mylar sheet, which in turn is surrounded by the adhesive side of the foam. Any soft thin material with high thermal resistance and low thermal conductivity can be preferably used as an interface between the sensor and the exterior, such as polyurethane foam (K=0.02 W/mC). Any support structure can incorporate the preferred insulation material.
A preferred power source for the patch includes natural thermoelectrics as disclosed by the present invention. In addition, standard lightweight thin plastic batteries using a combination of plastics such as fluorophenylthiophenes as electrodes can be used, and are flexible allowing better conformation with the anatomy of the BTT site. Another exemplary suitable power source includes a light weight ultra-thin solid state lithium battery comprised of a semisolid plastic electrolyte which are about 300 microns thick.
The system can have two modes: at room temperature the system is quiet and at body temperature the system is activated. The system can also have an on/off switch by creating a circuit using skin resistance, so only when the sensor is placed on the skin is the system activated. The patch can also have a built-in switch in which peeling off a conductive backing opens the circuit (pads) and turn the system on. In addition, when removed from the body, the patch can be placed in a case containing a magnet. The magnet in the case acts as an off switch and transmission is terminated when said patch is in the case.
FIGS. 19A1 to 19D are schematic views of preferred geometry and dimensions of support structures 180 and sensing device 182. Special geometry and dimension of sensors and support structure is necessary for the optimal functioning of the present invention. The dimensions and design for the support structure 180 are made in order to optimize function and in accordance with the geometry and dimensions of the different parts of the tunnel.
FIG. 19A1 shows support structure 180 working as a patch. The patch 180 contains sensor 182. The patch 180 may contain other hardware or solely the sensor 182. Exemplary sensor 182 is a flat thermistor or surface mount thermistor. The preferred longest dimension for the patch referred to as “z” is equal or less than 12 mm, preferably equal to or less than 8 mm, and most preferably equal to or less than 5 mm. The shortest distance from the outer edge of the sensor 182 to the outer edge of the patch 180 is referred to as “x”. “x” is equal to or less than 11 mm, preferably equal to or less than 6 mm and most preferably equal to or less than 2.5 mm. For illustrative purposes the sensor 182 has unequal sides, and distance “y” corresponds to the longest distance from outer edge of the sensor to outer edge of the patch 180. Despite having unequal sides, the shortest distance “x” is the determining factor for the preferred embodiment. It is understood that the whole surface of the sensor 182 can be covered with an adhesive and thus there is no distance between the sensor and an outer edge of a support structure.
An exemplary embodiment for that includes a sensor in which the surface touching the skin at the BTT site is made with Mylar. The Mylar surface, which comprises the sensor itself, can have an adhesive in the surface that touches the skin. In this case, the support structure that can include a piece of glue or an adhesive may be constructed flush in relation to the sensor itself. Accordingly in
As shown in FIG. 19A2, the sensor 182 has adhesive in its surface, to be secured to skin 11. The sensor then can be applied to the BTT site in accordance with the principles of the invention. The preferred distance “x” equal to or less than 2.5 mm allows precise pinpoint placement of sensor 182 at the main entry site of the tunnel and thus allows the most optimal signal acquisition, and it should be used for applications that require greatest precision of measurements such as during monitoring surgical procedures. Although a patch was used as support structure for the description of the preferred dimensions, it is understood that the same dimensions can be applied to any support structure in accordance with the principle of the invention including clips, medial canthal pads, head mounted gear, and the like.
The support structure and sensor are adapted to match the geometry and dimensions of the tunnel, for either contact measurements or non-contact measurements, in which the sensor does not touch the skin at the BTT site.
Preferred positions of sensors 182 in relation to the medial corner of the eye 184 are shown in
The preferred embodiments of support structures incorporated as patches and clips are preferably used in the hospital setting and in the health care field including continuous monitoring of fever or temperature spikes. Support structures incorporated as medial canthal pads or head mounted gear are preferred for monitoring hyperthermia, hypothermia and hydration status of recreational athletes, professional athletes, military, firefighters, construction workers and other physically intensive occupations, occupational safety, and for preventing wrinkle formation due to thermal damage by sun light.
Another preferred embodiment of the invention, shown in
As shown in
A variety of display devices and associated lenses for proper focusing can be used including liquid crystal display, LEDs, fiber optic, micro-projection, plasma devices, and the like. It is understood that a display device can be attached directly to the lens or be an integral part of the lens. It is also understood that a display device can include a separate portion contained in the lens rim or outside of the lens rim. Further, the two lenses and displays 296, 298 held within the lens rims 293, 297 can be replaced with a single unit which can be attached directly to the frame of eyeglasses 292 with or without the use of lens rim 293, 297.
Another preferred embodiment, as shown in
Sensing medial canthal pads can be preferably connected to attachment structure such as eyeglasses independent of the presence of specialized connecting or attachment devices mounted in said eyeglasses such as grooves, pins, and the like. This embodiment provides means for the universal use of sensing medial canthal pads in any type or brand of attachment structure. FIG. 30 shows a front perspective view of medial canthal pads 352 comprising an adhesive backing 354 for securing pad 352 to an attachment structure such as eyeglasses or another support structure. Adhesive surface 354 is adapted to match an area of eyeglasses that allow securing medial canthal pad 352 to said eyeglasses, such as for instance the area corresponding to regular nose pads of eyeglasses. Medial canthal pad 352 works as a completely independent unit and contains sensor 356, power source 358 and reporting device 360 electrically connected by wire 361,362. Reporting device 360 includes local reporting with visual devices (e.g., LED), audio devices (e.g., piezoelectric, voice chip or speaker) and remote reporting with wireless transmission.
Special nose pads are provided by the present invention for proper positioning a sensor at the BTT site.
It is understood that numerous special nose pads and medial canthal pads can be used in accordance with the principles of the invention including a pivotal hinge that allows pads to be foldable in total or in part, self-adjusting pads using a spring, pivoting, sliding in a groove, and the like as well as self-adjusting mechanisms which are adaptable to anatomic variations found in different races. It is understood that the modified nose pads are preferably positioned high in the frame, most preferably by connecting to the upper part of the lens rim or within 6 mm from the upper edge of the lens rim.
A variety of materials can be used including materials with super-adherent properties to allow intimate apposition of sensing devices to the BTT site. A variety of metallic wires exhibiting super-elastic properties can be used as the hinge assembly mechanism for allowing proper positioning of a sensing device with the BTT site. Medial canthal pads can be made of a flexible synthetic resin material such as a silicon rubber, conductive plastic, conductive elastomeric material, metal, pliable material, and the like so that appropriate apposition to the BTT site at the medial canthal area and proper functioning is achieved. It is also understood that the medial canthal pads can exhibit elastic and moldable properties and include material which when stressed is able to remain in the stressed shape upon removal of the stress. Any type of rubber, silicone, and the like with shape memory can also be used in the medial canthal pads and modified nose pad.
By greatly reducing or eliminating the interfering constituents and providing a high signal to noise ratio with a sensor adapted to capture thermal radiation from the BTT, the present invention provides the devices needed for accurate and precise measurement of biological parameters including chemical components in vivo using optical devices such as infrared spectroscopy. Moreover, the apparatus and methods of the present invention by enhancing the signal allows clinical useful readings to be obtained with various techniques and using different types of electromagnetic radiation. Besides near-infrared spectroscopy, the present invention provides superior results and higher signal to noise ratio when using other forms of electromagnetic radiation such as for example mid-infrared radiation, radio wave impedance, photoacoustic spectroscopy, Raman spectroscopy, visible spectroscopy, ultraviolet spectroscopy, fluorescent spectroscopy, scattering spectroscopy and optical rotation of polarized light as well as other techniques such as fluorescent (including Maillard reaction, light induced fluorescence and induction of glucose fluorescence by ultraviolet light), colorimetric, refractive index, light reflection, thermal gradient, Attenuated Total Internal Reflection, molecular imprinting, and the like. A sensor adapted to capture thermal energy at the BTE (Brain Thermal Energy) tunnel site provides optimal means for measurement of biological parameters using electromagnetic devices. The BTE tunnel is the physical equivalent to the physiologic BTT and is used herein to characterize the physics of the tunnel. The geometry and dimension on the skin surface are the same for the BTT and BTE tunnel.
The following characteristics of the BTE tunnel allow optimal signal acquisition. Skin at the end of the BTE tunnel is thin. With a thick skin radiation may fail to penetrate and reach the substance to be measured. Skin at the BTE tunnel is homogenous with constant thickness along its entire surface. Random thickness of skin as occurs in other skin areas prevent achieving the precision needed. The BTE tunnel has no fat. The intensity of the reflected or transmitted signal can vary drastically from patient to patient depending on the individual physical characteristics such as the amount of fat. A blood vessel in the end of the BTE is superficial, terminal and void of thermoregulatory shunts. In other parts of the skin the deep blood vessels are located deep and vary greatly in position and depth from person to person. The BTE tunnel has no light scattering elements covering its end such as bone, cartilage and the like. Thermal radiation does not have to go through cartilage or bone to reach the substance to be measured. The end of the BTE tunnel on the skin has a special but fixed geometry and is well demarcated by permanent anatomic landmarks. In other skin surfaces of the body, inconsistency in the location of the source and detector can be an important source of error and variability.
Far-infrared radiation spectroscopy measures natural thermal emissions after said emissions interact and are absorbed by the substance being measured. The present invention provides a thermally stable medium, insignificant number of interfering constituents, and a thin skin is the only structure to be traversed by the thermal emissions from the BTE tunnel before reaching the detector. Thus there is high accuracy and precision when converting the thermal energy emitted by the BTE tunnel into concentration of the substance being measured.
The natural spectral emission by BTE tunnel changes according to the presence and concentration of chemical substances. The far-infrared thermal radiation emitted follow Planck's Law and the predicted amount of thermal radiation can be calculated. Reference intensity is calculated by measuring thermal energy absorption outside the substance of interest band. The thermal energy absorption in the band of substance of interest can be determined via spectroscopic means by comparing the measured and predicted values at the BTE tunnel site. The signal is then converted to concentration of the substance measured according to the amount of thermal energy absorbed.
A sensor adapted to view the BTE tunnel provides means for measuring a substance of interest using natural brain far-infrared emissions emitted at the BTE tunnel site and for applying Beer-Lambert's law in-vivo. Spectral radiation of infrared energy from the surface of the BTE tunnel site corresponds to spectral information of chemical substances. These thermal emissions irradiated at 38 degrees Celsius can include the 4,000 to 14,000 nm wavelength range. For example, glucose strongly absorbs light around the 9,400 nm band. When far-infrared thermal radiation is emitted at the BTE tunnel site, glucose will absorb part of the radiation corresponding to its band of absorption. Absorption of the thermal energy by glucose bands is related in a linear fashion to blood glucose concentration in the thermally sealed and thermally stable environment present in the BTE tunnel.
The support structure includes at least one radiation source from infrared to visible light which interacts with the substance being measured at the BTE tunnel and a detector for collecting the resulting radiation.
The present invention provides method for measuring biological parameters comprising the steps of measuring infrared thermal radiation at the BTE tunnel site, producing output electrical signals representative of the intensity of the radiation, converting the resulting input, and sending the converted input to a processor. The processor is adapted to provide the necessary analysis of the signal to determine the concentration of the substance measured and for displaying the results.
The present invention includes means for directing preferably near-infrared energy into the surface of the skin at the end of the BTE tunnel, means for analyzing and converting the reflectance or back scattered spectrun into the concentration of the substance measured and support structure for positioning the light source and detector device adjacent to the surface of the skin at the BTE tunnel site.
The present invention also provides methods for determining the concentration of a substance with said methods including the steps of directing electromagnetic radiation such as near-infrared at the skin at the BTE tunnel site, detecting the near-infrared energy radiated from said skin at the BTE tunnel site, taking the resulting spectra and providing an electrical signal upon detection, processing the signal and reporting concentration of the substance of interest according to said signal. The invention also includes device and methods for positioning the light sources and detectors in stable position and with stable pressure and temperature in relation to the surface to which radiation is directed to and received from.
The present invention further includes devices for directing infrared energy through the nose using medial canthal pads, devices for positioning radiation source and detector diametrically opposed to each other, and devices for analyzing and converting the transmitted resulting spectrum into the concentration of the substance measured. The present invention also provides methods for measuring biological parameters with said methods including the steps of directing electromagnetic radiation such as near-infrared through the nose using medial canthal pads, collecting the near-infrared energy radiated from said nose, taking the resulting spectra and providing an electrical signal upon detection, processing the signal and reporting concentration of the substance measured according to said signal. The invention also includes means and methods for positioning the radiation sources and detectors in a stable position and with stable pressure and temperature in relation to the surface to which radiation is directed through.
The present invention yet includes devices for collecting natural far-infrared thermal radiation from the BTE tunnel, devices for positioning a radiation collector to receive said radiation, and devices for converting the collected radiation from the BTE tunnel into the concentration of the substance measured. The present invention also provides methods for measuring biological parameters with said methods including the steps of using the natural far-infrared thermal emission from the BTE tunnel as the resulting radiation for measuring the substance of interest, collecting the resulting radiation spectra, providing an electrical signal upon detection, processing the signal and reporting the concentration of the substance measured according to said signal.
A drug dispensing system including an infusion pump can be activated according to the level of the substance measured at the BTE tunnel, for example insulin can be injected automatically as needed to normalize glucose levels as an artificial pancreas.
Any substance present in blood which is capable of being analyzed by electromagnetic devices can be measured at the BTE tunnel. For example but not by way of limitation such substances can include exogenous chemicals such as drugs and alcohol as well as endogenous chemicals such as glucose, oxygen, lactic acid, cholesterol, bicarbonate, hormones, glutamate, urea, fatty acids, triglycerides, proteins, creatinine, aminoacids and the like. Values such as pH can also be calculated as pH can be related to light absorption using reflectance spectroscopy.
In accordance with
Infrared LEDs (wavelength-specific LEDs) are the preferred light source for this embodiment because they can emit light of known intensity and wavelength, are very small in size, low-cost, and the light can be precisely delivered to the site. The light source 420 emits preferably at least one near-infrared wavelength, but alternatively a plurality of different wavelengths can be used. The light source emits radiation 424, preferably between 750 and 3000 nm, including a wavelength typical of the absorption spectrum for the substance 432 being measured. The preferred photodetector includes a semiconductor photodiode with a 400 micron diameter photosensitive area coupled to an amplifier as an integrated circuit.
Arms of support structures 434 such as medial canthal pads are moveable and can be adjusted into different positions for creating a fixed or changeable optical path. Preferred substances measured include oxygen and glucose. The brain maintains constant blood flow, whereas flow in extremities change according to cardiac output and ambient conditions. The oxygen levels found in the physiologic tunnel reflects central oxygenation. The oxygen monitoring in a physiologic tunnel is representative of the general hemodynamic state of the body. Many critical conditions such as sepsis (disseminated infection) or heart problems which alter perfusion in most of the body can be monitored. Oxygen in the BTE tunnel can continuously monitor perfusion and detect early hemodynamic changes.
For example in the thermally sealed and thermally stable environment in the BTE tunnel 454, at 38.degree. Celsius spectral radiation 453 emitted as 9,400 nm band is absorbed by glucose in a linear fashion according to the amount of the concentration of glucose due to the carbon-oxygen-carbon bond in the pyrane ring present in the glucose molecule. The resulting radiation 453 is the thermal emission 452 minus the absorbed radiation by the substance 464. The resulting radiation 453 enters the infrared detector 444 which generates an electrical signal corresponding to the spectral characteristic and intensity of said resulting radiation 453. The resulting radiation 453 is then converted into the concentration of the substance 464 according to the amount of thermal energy absorbed in relation to the reference intensity absorption outside the substance 464 band.
The same principles disclosed in the present invention can be used for near-infrared transmission measurements as well as for continuous wave tissue oximeters, evaluation of hematocrit, blood cells and other blood components. The substance measured can be endogenous such as glucose or exogenous such as alcohol and drugs including photosensitizing drugs.
Numerous support structures can position sensors at the BTT site for measuring biological parameters. Accordingly,
It is understood that the sensing device can be an integral part of the support structure or be connected to any support structures such as using conventional fasteners including screw, pins, a clip, a tongue-groove relationship, interlocking pieces, direct attachment, adhesives, mechanical joining, and the like; and said support structures include patches, clips, eyeglasses, head mounted gear, and the like.
Various means to provide electrical energy to the sensing system were disclosed. The BTE tunnel offers yet a new way for natural generation of electrical energy. Accordingly,
Accordingly,
It is understood that other means to convert thermal energy from the BTE tunnel into electricity can be used. It is also understood that the surface of the eye and carbuncle in the eye can provide a thermal gradient and Seebeck effect, however it is much less desirable than using the skin at the end of the BTE tunnel since hardware and wires touching the surface of the eye and/or coming out of the eye can be quite uncomfortable and cause infection. It is yet understood that the cold end can include any relatively cold article including the frame of the glasses as well as the air.
Contrary to that numerous support structures disclosed in the present invention including eyeglasses can easily be adapted to provide in an unobtrusive manner the power generating system of the invention, for example by using a support structure such as eyeglasses for positioning the hot junction at the BTE site using medial canthal pads and positioning the cold junction on the nose using regular nose pads of eyeglasses. It is also understood that although the power generating system using Brain Thermal Energy was designed for powering the sensing system of the present invention, any other electrical device could be adapted to be supplied with energy derived from the Brain Thermal Energy tunnel.
Additional embodiments include support structures to position the sensor at the BTT site of animals. Many useful applications can be achieved, including enhancing artificial insemination for mammalian species by detecting moment of ovulation, monitoring herd health by continuous monitoring of brain temperature, detection of parturition and the like.
Accordingly,
Now, with reference to
The radiation sensor 504 views at least a portion of the BTT surface skin area 508 through an infrared radiation transparent window 502 and detect infrared radiation 506 from the BTT skin surface 508. The radiation sensor 504 is preferably a thermopile, but other radiation sensors may also be used such as pyroelectric detectors or any other radiation sensors that detect heat flux from the surface being evaluated. Exemplary window 502 materials include silicon and germanium. The sensor 504 is preferably mounted in an extension 510 which is shaped to match the dimension and geometry of the BTT area 508. The extension 510 can easily be positioned such that only the skin area 508 at the end of the BTT 518 may be viewed by the radiation sensor 504 wherein the skin area 508 is at substantially the same temperature as the brain temperature. Once in a position for the sensor 504 to view the BTT skin area 508, a button 522 is pressed to begin a measurement and the processing 514 within the housing 496 determines the brain temperature and display the value in a liquid crystal display 516 coupled to a sound device 524 for emitting an audio signal. A disposable cover may be used to cover any part of the apparatus in contact with the skin.
Although the temperature at the end of the BTT is substantially equivalent to the brain temperature based on the temperature of the cavernous sinus and cerebral blood, a variety of mathematical calculations and means can be used to determine the temperature at the BTT area including arterial heat balance, venous heat balance, and ambient temperature. It is understood that the BTT detector can contain a sensor for measuring ambient temperature and said measured ambient temperature be used for calculating temperature of the subject.
The temperature at the BTT area can be used as a reference for adjusting measurement acquired in other parts of the body outside the BTT area. The electrical equivalent of the BTT tunnel is an area of high voltage but low current, in which the voltage representing the temperature is virtually equal at the two ends of the tunnel. The high perfusion in the end of the BTT keeps a high temperature at the skin at the end of said end of the BTT.
The present invention also provides a method for detecting body temperature including the steps of providing a temperature detector positioned adjacent to the BTT during temperature detection and determining the temperature based on the radiation sensed at the BTT area. It is understood that the detector can remain in one position or move around the BTT area to identify the surface with the highest temperature.
A further method of detecting body temperature includes the steps of scanning a temperature detector across the BTT area and other areas in the head or in the contra-lateral BTT area and selecting the highest temperature, preferably selecting the highest temperature by scanning the right and the left BTT areas with the processor in the BTT detector determining and selecting the highest temperature.
Another method for identifying the highest temperature point in the BTT area can be found by scanning a radiation detector over the BTT area and having a processor adapted to select the highest reading and indicate that with an audio signal. The temperature detector 20 provides an audible beep with each peak reading.
In accordance with a further aspect of the present invention, the extension is adapted to fit on top of the eyelids. The portion of the extension 510 of the housing 496 in contact with the skin 508 can also have an inner concave surface that matches the eyelid contour. Alternatively, the portion of the conical extension 510 in contact with the skin 508 can have a convex surface to match the medial canthal area and upper lid above the medial corner of the eye.
It is also understood that the dimensions for pediatric use are about two thirds of the dimension for adult size, or even half or less than half of adult size especially in small children. Accordingly, the preferred sizes of the outer diameter of the extension for children are: for the radiation sensor viewing the general area the preferred outer diameter of the extension is equal to or less than 9 mm for viewing the general area of the BTT, equal to or less than 6 mm for viewing the general main entry point of the BTT, and equal to or less than 4 mm for viewing the main entry point of the BTT.
Besides the preferred round shape for the end 524 of extension 510,
It is understood that although an extension is the preferred embodiment with the sensor not contacting the skin, an infrared sensor probe adapted to touch the skin at the BTT area can also be used.
Now in reference to the thermal imaging systems of the present invention,
The infrared radiation detector converts the incident radiation that includes the BTT area into electrical energy which is amplified. The detector 570 is responsive to infrared radiation to provide an output signal and discrete points (only) related to the intensity of the thermal energy received from the BTT area and the surrounding area around the BTT area.
The discrete points are imaged and each point source must have enough energy to excite the radiation detector material to release electrons. Any point size can be used, but preferably with a size between 1 and 2 mm in diameter. When using an angle of 1.3 mrads, the BTT ThermoScan can capture an instantaneous image from a point size of approximately 1 mm diameter at a distance of 1 m from the detector. It is understood that any spatial resolution for optimal capturing of the BTT image can be used, but it is preferably between 1.0 and 1.6 mrad. The camera 562 of the BTT ThermoScan 560 has a field of view adapted to view the BTT area. Discrete points are further converted into an image of the face that includes the BTT area in the medial corner of the eye and upper eyelid. The screening function of the BTT ThermoScan is based on the temperature at the BTT area, either absolute temperature or the differential temperature of the BTT area in relation to a reference.
The electrical response to the thermal radiation can be displayed on the monitor as intensity, with a strong signal producing a bright (white) point as seen in
It is understood that a variety of lenses, prisms, filters, Fresnel lenses, and the like known in the art can be used to change the angle of view or optimize signal acquisition and capture of thermal energy flux from the face and the BTT area. The lens of the BTT ThermoScan 560 is preferably perpendicular to the plane of the human face or of the BTT area being viewed.
The radiation detector material in the BTT ThermoScan 560 is preferably sensitive to radiation with wavelength ranging from 8 to 12.mu.m. The BTT ThermoScan 560 has a temperature span set between 2 to 5 degrees Celsius and is extremely sensitive and adapted to discern temperatures to within 0.008 degrees Celsius to 0.02 at a range of 1 meter. Temperature measurements can be based on radiometric means with built-in electronics or by differential using a reference such as a black body. Although the system can be uncooled, to maximize the efficiency of the detector and achieve an optimum signal to noise ratio the detector can be cooled using solid state means, liquid nitrogen, evaporation of compressed argon gas, piezoelectric components, and the like.
Many radiation detectors capable of detecting infrared waves are being developed including silicon based, solid state systems, and microbolometers, and all said systems new or to be developed in the future can be used in the apparatus of the present invention to detect thermal radiation from the BTT with the display of a corresponding image of the BTT in a monitor.
An exemplary infrared detector system includes a microbolometer which is fabricated on silicon substrates or integrated circuits containing temperature sensitive resistive material that absorbs infrared radiation, such as vanadium oxide. The incident infrared radiation from the BTT area is absorbed by the microbolometer producing a corresponding change in the resistance and temperature. Each microbolometer functions as a pixel and the changes in electrical resistance generate an electrical signal corresponding to thermal radiation from the BTT area that can be displayed in a screen of a computer.
The display of the image of the BTT is the preferred embodiment of the invention, but the present invention can be implemented without display of an image. Radiation coming from the BTT can be acquired by the radiation sensors aforementioned and the temperature of the BTT area can be calculated based on the electrical signal generated by the radiation sensor using a reference. Any means to detect thermal radiation and/or temperature from the BTT area can be used in accordance with the principles of the invention.
Besides the easy manipulation of temperature at the skin level outside the BTT area, significantly lower temperatures are found in the areas outside the BTT as shown in the image on the screen, and depicted in the photos of
It is understood that a variety of signal conditioning and processing can be used to match the temperature areas outside the BTT area to a value that corresponds to the BTT area, and those methods also fall in the scope of the invention. Image outside the BTT area as seen more like a blur compared to the BTT area and superimposition of images that include the BTT area can also be used for achieving higher level of accuracy during temperature measurements. Comparing a radiation pattern outside the BTT area with the BTT area without necessarily creating an image of the BTT area can also be used for accurate and precise temperature measurement and evaluation of the thermal status of the body in accordance with the principles of the invention. Any method or device used for temperature evaluation or evaluation of the thermal status that is based on the temperature level or thermal radiation present in the BTT area by generating or not generating an image falls within the scope of the present invention.
Exemplarily, passenger 592 is looking at the camera 582 for sensing the thermal radiation from the BTT area 590, with said passenger 582 holding his/her eyeglasses since for the camera 582 to precisely view the BTT area 590 the eyeglasses have to be removed. If someone goes by the camera 582 without a thermal image of the BTT 590 being acquired an alarm will be activated. Likewise, if someone has a temperature disturbance an alert indicative of said temperature disturbance is activated.
A facility that is of strategic importance such as a government building, military bases, courts, certain factories and the like can also benefit from screening for temperature disturbances. As shown in
Now referring to
To enhance the image generated by the BTT ThermoScan, the method further includes aligning the BTT area with the field of view of the infrared detector and by removing eyeglasses during thermal detection of the BTT area.
Now in reference to
The detection of the main entry point of the BTT can also be done automatically. Accordingly,
It is also an object of the invention to provide methods and devices for treating and/or preventing temperature disturbances. As shown in
Accordingly, another object of this invention is to provide a new and novel BTT thermal pad for the application of cold or heat to the BTT area for cooling or heating the brain.
A further object of this invention is to provide a new and novel BTT thermal pad which covers the entrance of the BTT area, which may extend to other areas of the face. However, since the brain is insulated on all other sides but at the BTT entrance, the cooling is only external and does not reach the brain, which could be at “frying” temperature despite the external cooling sensation. Considering that, a preferred embodiment includes an extended BTT thermal pad covering the face in which only the BTT area is exposed to the cold and the remainder of the extended BTT thermal pad covering the face is insulated, preventing the warming up of the gel or ice placed inside the bag. The BTT thermal pad container can include a radiant heat-reflecting film over various portions thereof, and an insulator over the same or other portions and which together facilitate directional cooling. Thus, only heat conducted by the BTT is absorbed as the BTT is cooled.
The BTT thermal device applied to the BTT area promotes selective brain cooling or selective brain heating for treating hyperthermia and hypothermia respectively. The brain, which is the most sensitive organ to thermally induced damage, can be protected by applying heat via the BTT during hypothermia or removing heat during hyperthermia. The cooling or heating is selective since the temperature of the remaining body may not need to be changed, this is particularly important when cooling the brain for treating patients with stroke or any brain damage. The majority of the brain tissue is water and the removal or application of heat necessary to cool or heat the brain can be precisely calculated using well known formulas based on BTU (British thermal unit). A BTU is the amount of energy needed to raise the temperature of a pound of water 1 degree F., when a pound of water cools 1 F, it releases 1 BTU.
The BTT thermal pad for therapeutic treatment of excessive heat or excessive cold in the brain preferably includes a bag having a substantially comma, banana, or boomerang shape, with said bag in complete overlying relationship with the entire entrance of the BTT, said bag including an outer wall and an inner wall defining a sealed cavity to be filled with ice, gel-like material, solid material, and the like, for cooling or heating the BTT skin area overlying the entrance of the BTT.
An exemplary brain cooling or brain heating device includes hot and cold pad or pack adapted to fit and match the special geometry of the entrance of the BTT and comprising a preferably flexible and sealed pad and a gel within said pad, said gel being comprised of a mixture of water, a freezing point depressant selected from the group consisting of propylene glycol, glycerine, and mixtures thereof associated with other compounds such as sodium polyacrylate, benzoate of soda, hydroxibenzoate, and mixtures thereof and a thickening agent. Any other cooling or heating device or chemical compounds and gels including a combination of ammonium nitrate and water can be used as cooling agent as well as heating agents such as a combination of iron powder, water, activated carbon, vermiculite, salt and Purge natural mineral powder. Those compounds are commercially available from many vendors (e.g., trade name ACE from Becton-Dickson).
In use the BTT thermal pad would be put into a freezer or other chilling device for use as a cold compress or would be put into hot water to be used as a hot compress. The BTT thermal pad preferably comprises a tough flexible envelope of plastic material. The material within the BTT thermal pad is preferably a gel which will maintain its gel-like consistency over a wide range of temperatures. There exist many gels which can be cooled to freezing and which absorb heat during warmup. There are a number of different types of such gels. Some of them freeze solid, and some are flexible even at 0 degrees F. Cold packs such as a frozen water-alcohol mixture can also be used. Alternatively, a BTT thermal pad includes a bag having inner and outer walls lined interiorly with plastic which define a cavity to be filled with ice through an opening in the bag. In this instance the bag is preferably sealed with a rubber material.
Although flexible plastic is described as a preferred material for containing the gel, it is understood that any material or fabric can be used including vinyl, cotton, rayon, rubber, thermoplastic, synthetic polymers, mixtures of materials, and the like. The size and shape of the BTT pad structure is adapted to fit the special anatomy of the recess between eye and nose and for matching the special geometry of the entrance of the BTT.
Any cooling or heating device known in the art can be used in the BTT pad treatment device including hot or cold water flowing through tubes that are adapted to carry or deliver heat to the BTT area. The tubes can be mounted in any head gear or the frame of eyeglasses, pumping mechanisms can be mounted in the head gear or eyeglasses for providing a continuous flow of water through the tubes. The BTT pad can be connected to tubes which have connectors for joining to a water temperature control and circulating unit in the head gear or eyeglasses. Hot or cold liquid is circulated through tubes which are in communication with each other and which deliver or remove heat from the BTT.
Elastic band or hook and loop fastener can be used for securing the BTT pad in position. Any of the support structures mentioned herein can be used to secure the BTT pad in position including a piece of glue. For example, the BTT pad can include a clip like mechanism or the BTT thermal pad can be secured to the frame of eyeglasses. Nose pads of eyeglasses or modified nose pads of eyeglasses can include cooling or heating devices for delivering or removing heat from the BTT. A BTT thermal pad can include a stick mounted in the pad that can held by hand and manually placed in the BTT area, for example held by a player during a break in the game to reduce the temperature in the brain, or for warming up the brain of a skier during a winter competition.
An alternative embodiment includes a BTT thermal pad attached to a head gear for supplying water to evaporatively cool the BTT area. In this instance the cold water is generated by evaporative cooling in the headband and forehead and upper portion of a wearer's head.
Any cooling or heating device can be used to cool or heat the BTT area for selective brain cooling or brain heating, preferably using a moldable device that conforms to the anatomy of the region at the entrance of the BTT, with directional temperature control properties for cooling or heating the skin at the entrance of the BTT. Any of the devices for heating or overheating or for cooling, including electrical, chips, semiconductor, polymers, and the like known in the art as well as described by Abreu in U.S. Pat. No. 6,120,460; No. 6,312,393 and U.S. Pat. No. 6,544,193, herein incorporated in their entirety by reference, and other pending applications by Abreu can be adapted in support structures for positioning at the BTT entrance and used for cooling or heating the brain.
The present invention provides a moldable BTT thermal pad or BTT thermal pack in a packaging arrangement that can provide surfaces of differing thermal conductivities and heat reflecting properties so as to prolong the useful cooling/heating time thereof. The construction and materials of the BTT thermal pad or BTT thermal pack permits the molding of its shape and the retention thereof to the BTT site on the skin between the eye and nose. The materials disclosed herein can remain flexible plastic for temperatures in the range of −10.degree. C. to 140.degree. C.
Referring to
It is understood that a ring shape surrounding the eye can also be used or a shape that includes other parts of the face/forehead as long as there is conformation and apposition of part of the BTT thermal pack to the BTT area. The preferred shape and dimension matches the special geometry of the BTT area described herein.
The BTT thermal pack is preferably moldable and the container or bag constructed with materials that are deformable and otherwise pliable over the temperature range of use so as to conform to the anatomy of the BTT area. A central convex area in the pack allows for intimate interaction and thermal energy transfer at the entrance of the BTT, but it is to be recognized that the specific shape of the convex area of the BTT cold/heat pack itself can be slightly varied according to the ethnic group.
The brain cooling or brain heating device in accordance with the principles of the invention includes hot and cold pad or pack adapted to fit and match the special geometry of the entrance of the BTT and comprising a preferably flexible and sealed pad and a gel within said pad, with the surface touching the skin having a substantially convex shape. Accordingly,
A tube fit to match the special geometry of the BTT site and anatomy of the region with circulating water can also be use for selectively cooling or heating the brain.
The BTT thermal pack can include a bag so as to avoid direct contact with the skin depending on the chemical compound used, such as heating agent to prevent any thermal injury to the skin.
It is understood that a combination temperature sensor and BTT cold/heat pack can be implemented and positioned in place using the support structures described herein such as eyeglasses and any head mounted gear. The nose pads of eyeglasses can have a combination of a heat flow sensor to determine how fast heat is being pulled. The gradient for instance across a thin piece of Mylar indicates the direction of heat flow. It is also understood that the right nose pad of the eyeglasses have a temperature sensor and the left side has the cooling/heating device that applies or removes heat according to the temperature measured on the opposite side.
It is also understood that many variations are evident to one of ordinary skill in the art and are within the scope of the invention. For instance, one can place a sensor on the skin at the BTT site and subsequently place an adhesive tape on top of said sensor to secure the sensor in position at the BTT site. Thus in this embodiment the sensor does not need to have an adhesive surface nor a support structure permanently connected to said sensor.
A plurality of hand held devices with non-contact or contact sensors can measure the brain temperature at the BTT for single or continuous measurement and are referred to herein as Brain Thermometers or BrainTemp devices. Accordingly,
An exemplary lens system for viewing thermal radiation coming from the BTT can include exemplarily 25 sensors for reading at 1 inch from the tip of the sensor to the skin at the BTT entrance and 100 sensor array for reading radiation coming from a distance of 3 inches between skin at the BTT and sensor tip. Preferably a five degree field of view, and most preferably a two to three degree field of view, and yet even a one degree of field view is used to see the main entry point of the BTT. The spot size (view area) of the infrared sensor is preferably between 1 and 20 mm in diameter and most preferably between 3 and 15 mm in diameter which allows the infrared sensor to receive radiation from the BTT entrance area when said sensor is aimed at the BTT entrance area which corresponds to the bright spots in
The array is adapted to receive the temperature of the BTT area. The temperature signal received is less than the whole face and is not the temperature of the face, nor the temperature of the forehead. The temperature signal comes from the BTT, one particular area of special geometry around the medial corner of the eye and medial aspect of the upper eyelid below the eyebrow. This said temperature signal from the BTT can be acquired by contact sensors (e.g., thermistors), non contact sensors (e.g., thermopile), and infrared thermal imaging. This said temperature signal can be fed into a processor to act upon an article of manufacturing that can remove or transfer heat as shown in
A retractable ruler 1046 is mounted in the housing 1032 and the tip of said ruler can rest on the face and used for assuring proper distance and direction of the housing in relation to the BTT for optimal view of the BTT area. It is understood that any measuring and positioning means for optimizing view of the BTT by the sensor can be used and are within the scope of the present invention. It is understood that any positioning device to establish a fixed relationship between the sensor and BTT are within the scope of the invention.
The temperature signal from sensor 1052 can be converted to an audio signal emitted by the piezoelectric device 1062 with said audio frequency proportional to the temperature level measured. In addition processor 1056 in the housing 1050 is adapted to lock in the highest frequency audio signal (which represents the highest temperature) while the user scans the BTT area. Furthermore, LED 1060 in the housing 1050 can be activated when the highest temperature level is reached, and then the value is displayed in display 1058.
It is understood that any article of manufacture that transfers heat or removes heat from the body in a direct or indirect fashion can be used in accordance with the principles of the invention. Accordingly
In the embodiment in which a contact sensor touching the skin is used, the probe head can be covered with a disposable cap, such as a piece of polymer preferably with good thermal conductivity, with the shape of the disposable cap to match the shape of the various probes in accordance with the principles and disclosure of the present invention.
In addition to measuring, storing, and transmitting biological parameters, the various apparatus of the present invention such as patches, eyewear, rings, contact lens, and the like include an identification and historical record acquisition and storage device for storing the user's identification and historical data preferably using a programmable rewritable electronic module in which data can be changed, added, or deleted from the module. The identification and historical data alone or in conjunction with the biological data (such as brain temperature and chemical measurements as glucose level and presence of antibodies) are transmitted preferably by wireless transmission to a monitoring station. Accordingly
Each eye ring 1501 has a unique serial number permanently or temporarily embedded to identify the animal remotely. A 24 hour temperature log is sent at each transmission, most preferably 6-12 times per day. A unique one-way statistical broadcast network architecture allows all members of the herd to share one frequency and one set of data receivers. The receiver is designed to receive temperature telemetry data from a network of livestock eye ring telemetry units and forward it to a collection computer for storage, display, and monitoring.
Although various communication and power systems are shown in
It is understood that besides an active system with a battery working as the power source, a passive system in which the ring 1501 is powered by an external source such as electromagnetic induction provided by collar 1520 or antenna 1524 can be used. It is further understood that a hybrid system that includes both a power source comprised of battery 1503 and a passive system in module 1504 can be used in which module 1504 contains an antenna for receiving electromagnetic energy from module 1508 of collar 1520. In this embodiment the active part of the system using the memory in module 1504 powered by battery 1503 collects data from a sensor 1502 (e.g., thermistor) and stores the data in a memory chip in module 1504. The passive system containing antenna in module 1504 can be also activated when the four legged creature passes by a coupling antenna 1524, such as for instance an antenna placed in feed lots. After there is a coupling between the passive system 1504 in the ring 1501 and the external antenna 1524 in the feedlot, the data stored in the memory chip of module 1504 of the ring 1501 is received by the external antenna 1524 and transferred to a second memory chip 1523 that is part of the module external antenna 1524. The processor of module 1504 in the ring 1501 is adapted to transfer the stored data any time that there is a coupling with the external antenna 1524. A variety of inductive coupling schemes previously mentioned can be used for powering and collecting data from eye ring 1501 by antenna 1523 and 1509.
The data from a plurality of mammals (e.g., cattle) is transmitted to a receiving system. Preferably only one animal transmits at a specific time (equivalent to having only one animal in the system) to avoid data collisions in the form of interference that prevents successful wireless transmission of the biological parameters. Two exemplary schemes can be used, polling and broadcast. The polling approach requires each animal to be equipped with a receiver which receives an individual serial number request for data from a central location and triggers that animal's transmitter to send the data log. The other approach is a broadcast system, whereby each animal independently broadcasts its data log. The problem is to avoid collisions, that is, more than one animal transmitting at a time, which could prevent successful data transfer. Each animal transmitter will preferably transmit at a certain time and the receiver is adapted to receive the signal from each animal at a time.
The ring 1501 can yet include a solar battery arranged to capture sun light, digital transmission 16 bit ID# to identify the animal and track the animal throughout life. Preferred dimensions for outer diameter of ring 1501 for use in livestock are between 40 and 45 mm, preferably between 35 and 40 mm, and most preferably between 30 and 35 mm or less than 30 mm. For large animals such as an elephant, such as to detect moment of ovulation for artificial insemination and birth in captivity, the preferred outer diameter is between 90 and 100 mm, preferably between 75 and 90 mm, and most preferably between 50 and 75 mm or less than 50 mm. Preferred largest dimension of ring including circuit board and battery for livestock is between 15 and 20 mm, preferably between 10 and 15 mm, and most preferably less than 10 mm, and for large animals a factor of 10 to 15 mm is added to achieve optimal dimensions. The preferred height of the ring 1501 for livestock is between 9 and 12 mm, preferably 6 and 9 mm, and most preferably less than 5 mm, and for large animals a factor of 5 mm is added to achieve optimal dimensions. The preferred embodiment includes hardware disposed in one quadrant of the ring which contains the sensor and is located in the inferior eyelid pocket.
An alarm is activated when certain pre-set temperature limits are reached. The system of the invention can also be used with temperature being transmitted in real time for detecting the moment of heat in animals, which starts when the body temperature of the animal starts to rise. The method includes detection of heat, and then inseminating the animals preferably between 6 to 12 hours after initial detection of heat, and most preferably between 4 and 8 hours after heat detection.
Preferably the temperature data stored over time (e.g., 24 hours) by module 1504 or 1508 is then downloaded to a computer system such as computer 1526 adapted to identify thermal signatures. Thermal signatures are representations of the temperature changes occurring over time and that reflect a particular biological condition. Exemplary thermal signatures are depicted in
A plurality of antenna reception scheme can be used.
Although a multiple antenna scheme is shown in
When using a rewritable or programmable identification serial number, the eye ring 1501 can be reused and a new serial identification number programmed and written for said eye loop or eye ring 1501.
Although a ring in the eyelid pocket is shown, it is understood that another method and device includes a temperature signal coming from the BTT of cattle external to the eye which is located in the anterior corner of the eye (corner of the eye in animals is located in the most frontal part of the eye) with said signal being captured by contact or non contact temperature sensors as well as thermal imaging.
The signal from eye ring 1501 can preferably automatically activate another device. By way of illustration, a sprinkler system can be adapted to be activated by a radio signal from eye ring 1501 with said sprinkler system spraying cold water and cooling off the animal when a high body temperature signal is transmitted by eye ring 1501.
A variety of diseases can be monitored and detected by the apparatus of the invention. By way of illustration, a characteristic increase in brain temperature can detect foot-and-mouth disease, babesiosis, botulism, rabies, brucellosis, and any other disorder characterized by changes in temperature as well as detection of disorders by chemical and physical evaluation such as detection of prions in the eyelid or eye surface of an infected animal using antibodies against such prions and creating an identifiable label such as fluorescence or by generating a mechanical or electrical signal at the time of antigen-antibody interaction. Prions can cause bovine spongiform encephalopathy known also as “mad cow” disease and such prions can be present in the eye and can be detected by using an immobilized antibody contained in the eye ring against such prion or a product of such prion. By detecting mastitis (or an animal with fever) which is scheduled for milking, the present invention provides a method to prevent contaminating other animals being milked by generating a sequence for milking in which the animal with fever is milked last. This will avoid contaminating equipment with a sick animal and with said equipment being sequentially used in other healthy animals.
The present invention provides continuous monitoring of animals 24 hours a day from birth to slaughter with automatic analysis and detection of any disease that can cause a threat to human health or animal health, besides identification and location of the sick animal. Therefore with the present invention an animal with disease would not reach the consumer's table. The present invention therefore includes a method to increase food safety and to increase the value of the meat being consumed. The system of continuous disease monitoring is called DM24/7 (disease monitoring 24/7) and includes monitoring the biological variable 24 hours seven days a week from birth slaughter, feeding the information into a computer system and recording that information. Any meat coming from an animal monitored with DM24/7 receives a seal called “Monitored Meat”. This seal implies that the animal was monitored throughout life for the presence of infectious diseases. Any user buying “Monitored Meat” can log on the internet, and after entering the number (ID) of the meat which can be found in the package of the meat being purchased. Said user can have access to the thermal life and biological monitoring of the animal and for the presence of fever or disease of the animal which the meat was derived from. The method and device includes a video stream associated with the ID of the animal with said video or pictures showing the farm and information on the farm where the animal came from or the meat pack facility where the animal was processed, providing therefore a complete set of information about the animal and conditions in which such animal was raised. Besides viewing over the internet, at a private location such as at home, the system may also provide information at the point of sale. Accordingly, whenever the user purchases the product and a bar code for the product for instance is scanned, a video or photos of the farm or the company packing the meat appear on a screen at the point of sale. This method can be used when purchasing any other product and preferably allows the consumer to use idle time in the cashier's station to become more familiar with the product purchased.
Preferably the ring has a temperature sensor covered by insulating material (eg. polyurethane) in one end and with an exposed surface at the other end. The preferred measuring method uses the measuring surface facing the outer part of the anatomy of the eye pocket and the insulating part facing the inner part of the eyelid pocket.
The eye ring contains memory means for storing on a permanent or temporary basis a unique identification number that identifies the animal being monitored. The ID code in the processor of the ring is transmitted to a receiver as an individual number only for identification and tracking purposes or associated with a temperature value or other biological variable value. The memory chip in the ring can also contain the life history of the animal and historical data including weight, vaccines, birth date, birth location, gender, diseases, genetic make up, and the like.
Range of the entrance of BTT area is about 30 square cm and the general main entry point is 25 square cm and encompasses the medial corner of the eye and the area of the eyelid adjacent to the eyelid margin. The correlation coefficient between temperature at the BTT area and the core temperature reflecting the thermal status of the brain is 0.9. Instead of using the whole face, the method for infrared or thermal imaging sensing as well as contact sensor includes a temperature signal which comes specifically from the BTT area, and the hottest spot in BTT area is then located and used as a source signal to activate another device or to deploy an action.
It is understood that an infrared thermal imaging camera can also be used and the point source emitting the highest amount of radiation from the entrance of the BTT is selected by the processor in the camera and the temperature level corresponding to the point source with highest thermal energy is displayed in the display. Exemplary infrared cameras include the BTT Thermoscan of the present invention.
The BTT Thermoscan of the present invention is adapted to view the entrance of the BTT around the medial corner of the eye, with the view of the sensor, by way of a lens, matching the entrance of the BTT area displayed in
Now in accordance with another preferred embodiment of the present invention shown in
When applied to the skin the VELCRO Patch works as one piece with durable and disposable parts connected by the hook and loop material and no hardware is visible on the surface of the durable part with the exception of a reporting device such as a LED to alert the user when the biological parameters are out of range. Accordingly
VELCRO Patch of the present invention can further include attachment structure for attaching lenses to said VELCRO Patch, herein referred as VELCRO Eyewear. Accordingly
The present invention provides a method for optimizing fluid intake to achieve euhydration and avoid dehydration and overhydration. The present invention provides a continuous noninvasive core temperature monitoring, and when the temperature reaches certain pre-set levels such as increased temperature which reflects increased heat stored in the body, then by ingesting fluid the temperature can be lowered. Brain temperature reflects the hydration status and dehydration leads to an increase in the core (brain) temperature. The method in accordance with the present invention includes an algorithm for use in the situation of dehydrated, sedentary people exposed to heat (as illustrated by the excess mortality during heat waves), and people during physical activities. The invention showed that ingestion of 4 ounces of water every hour after body temperature reaches 100.4 degrees F. will lower the body temperature to 98.6 degrees F. and will keep the body temperature at lower than 99.5 degrees F. thus preventing the dangers of heat stroke. In case of athletes in athletic activities such as cycling, the invention showed that ingestion with fluid containing carbohydrates and minerals (e.g., trade name PowerAde of the Coca-Cola Company) can keep peak performance with ingestion of 6 to 8 ounces when the temperature at the BTT reaches 99.3 degrees Fahrenheit and performance is maintained with ingestion every 1 to 2 hours. A variety of algorithms for use in the situation of athletes at risk of overheating, can be created based on the principle of the invention. Special size containers for fluid or water can be used by an athlete who is aware of the fluid intake needed during a competition.
A method and algorithm to couple temperature (hypothermia) to nourishment (malnutrition) in elderly and in anorexia nervosa can be created, with the temperature level indicating malnutrition and further indicating what food to ingest to maintain adequate temperature. It is further understood that foods can be developed based on body temperature to achieve optimal nutritional value—fresh and frozen, or processed foods. It is yet understood that temperature changes indicating ovulation can be used as a method to create foods that increase fertility by identifying what food articles increase ovulation.
The present invention also provides methods and devices for evaluating diet such as caloric restriction in which the temperature indicates the metabolism and therefore a lower basal temperature indicates reduced metabolism and metabolic waste products including monitoring carbohydrate intake and metabolism. The present invention also provides methods for monitoring hypoglycemia in diabetes in which lowering of the temperature is a predictor of a hypoglycemic event. The invention also provides methods for detecting pulmonary infarction and cardiac events which are associated with a particular increase in temperature. Any condition which is associated with a change in temperature can be predicted and detected by the present invention from pregnancy disorders coupled to hypothermia to hyperthermia in head trauma.
The present invention provides a variety of other benefits. Other exemplary benefits include: 1. monitoring Multiple Sclerosis since increase in brain temperature can lead to worsening of the condition, and a corrective measure can be taken when the present invention identifies such increase in temperature, such as by drinking cold liquids at the appropriate time or cooling off the brain as previously described, 2. significant differences between left and right BTT can indicate a pathological central nervous system condition, 3. detecting increased brain temperature to reinforce diagnosis of meningitis or encephalitis and thus avoid excess use of lumbar tap in people without the infection, and 4. Young babies cannot regulate their body temperature in the same way that adults do and can easily become too hot. Sudden Infant Death Syndrome (SIDS) is more common in babies who have become overheated. By monitoring babies' temperature the present invention can alert parents in case the baby's temperature increases.
A receiver receiving signal from the sensor system of the present invention can be external or implantable. When implantable inside the body the receiver can be powered by magnetic induction externally or batteries recharged externally. The receiver receives the signal from a temperature sensor, glucose sensor, or the like and retransmits the signals for further display.
Any transmitter of the present invention can be integrated with Bluetooth, GRPS data transmission, and the like. The signal from the transmitter then can be captured by any Bluetooth enabled device such as cell phones, electronic organizers, computers, and the like. Software of the cell phone can be modified to receive the coded signal from a transmitter. Algorithm in the receiver will decript the signal and display the value. A cell phone can have an auto dial to call a doctor for example when fever is noted. It is understood that the signal from a cell phone or a signal directly from the transmitter of the support structure can be transmitted to a computer connected to the internet for further transmission over a distributed computer network.
The prior art used facial skin temperature as detecting means for monitoring body temperature. As seen in
Now referring to the previously described automated climate control system, an exemplary embodiment will be described in more detail. Although this exemplary preferred embodiment will be described for climate control in the cabin of a transportation vehicle (e.g., car) it is understood that the method, device and system can apply to any confined environment such as home, work place, a hotel room, and the like in which the temperature inside the confined environment is adjusted based on the temperature at the BTT for achieving thermal comfort for the subject inside the confined environment.
The temperature measurement at the BTT represents the thermal comfort of the body. Investigation by the present invention showed that the thermal comfort of the body is reduced as the temperature of the body increases or decreases reflected by a change in brain temperature at the BTT. Thermal comfort of a human being is reflected by the skin temperature at the BTT, with higher skin temperature at the BTT generating a hot body sensation while a lower skin temperature at the BTT generates a cold body sensation. In order to achieve thermal comfort for the occupants of a cabin the system of the invention manages cabin thermal comfort from the temperature signal generated at the BTT. The present invention preferably uses a particular specialized area in the face, and not the whole face to manage the cabin temperature and cabin thermal comfort. The present invention system preferably monitors temperature in less than the whole face which causes an optimal control of the heating and cooling of the cabin to achieve thermal comfort of the occupant of the cabin.
Since thermal comfort is reflected in the brain temperature adjusting the climate cabin based on the temperature of the BTT will provide a thermally comfortable environment for the occupant of the cabin. The BTT temperature is set for controlling the HVAC (heater-air conditioner) and other parts of the vehicle previously mentioned such as seats, carpets, and the like, which are adjusted to maintain the occupant's thermal sensation in a comfortable state. In particular, articles in contact or adjacent to the body are used to automatically remove or apply heat to the occupant's body based on the BTT signal. To further improve thermal comfort, the system includes a temperature sensor in the cabin for detecting cabin temperature. Accordingly,
Yet another embodiment according to the present invention includes a support structure containing a sensor to measure biological parameters connected to a nasal strip for dilating airways of humans such as Breathe Right (commercially available under the trade name BreatheRight) and for dilating airway passages of animals (commercially available under the trade name Flair). Exemplary air dilator nasal strips were described in U.S. Pat. Nos. 5,533,503 and 5,913,873. The present invention incorporates airway dilators into patches for biological monitoring. The present invention can be an integral part of an airway dilator. The airway dilators can be an extension of the present invention. The coupling of a patch measuring biological parameters and an air dilator is convenient and beneficial since both are useful in the same activities. Nasal airway dilators are beneficial during sleeping, in athletic activities, or when suffering from a cold or respiratory infections and the patch of the present invention is used during sleeping, monitoring temperature changes in athletic activities, and monitoring fever during respiratory infections. Both nasal airway dilators and the patch of the present invention use an adhesive in its backing to secure to the skin and both are secured to the skin over the nasal bones, the patch of BTT located in the superior aspect of the nasal bone and the air dilator preferably in the inferior aspect of the nasal bone. The nasal airway dilator extension of the patch of the present invention is referred to herein as BioMonitor Dilator (BMD). Accordingly,
Another embodiment includes a plurality of kits shown in
Another embodiment includes shoes with temperature sensor for detecting cold and with a radio transmitter to transmit the signal to a receiver (e.g., Watch). The signal from the shoe in conjunction with the signal from the TempAlert at the BTT provides a combination of preventive device against both frostbite and hypothermia.
It is understood that the support structure such as a patch may house vapors and when the outer surface of the patch is scratched mentholated vapors can be released to help soothe and relieve nasal congestion, which can be convenient when monitoring fevers with the patch.
It is also understood that steel or cooper can be placed on top of a sensor to increase thermal conductivity as well as any other conventional means to increase heat transfer to a sensor.
It is understood that any electrochemical sensor, thermoelectric sensor, acoustic sensor, piezoelectric sensor, optical sensor, and the like can be supported by the support structure for measuring biological parameters in accordance with the principles of the invention. It is understood that sensors using amperometric, potentiometric, conductometric, gravimetric, impedimetric, and fluorescent systems, and the like can be used in the apparatus of the invention for the measurement of biological parameters. It is also understood that other forms for biosensing can be used such as changes in ionic conductance, enthalpy, and mass as well as immunobiointeractions and the like. It is also understood that new materials and thermally conductive liquid crystal polymers that produce a response in accordance to temperature can be used in the invention and positioned at the BTT site.
The foregoing description should be considered as illustrative only of the principles of the invention. Since numerous modifications and changes will readily occur to those skilled in the art, it is not desired to limit the invention to the exact construction and operation shown and described, and, accordingly, all suitable modifications and equivalents may be resorted to, falling within the scope of the invention.
Sensing device 2000, for purposes of illustration, is shown as comprised of three parts, body 2002, arm 2004, and measuring portion 2006. Body 2002 is demarcated by line EF and line CD. Arm 2004 is demarcated by line CD and line AB. Measuring portion 2006 is demarcated by line AB, and works as the free end of sensing device 2000. Arm 2004 is connected to measuring portion 2006 and to body 2002. Body 2002 of the sensor system 2000 can preferably comprise a plate configuration, said plate preferably having essentially flexible characteristics so as to be molded and/or to conform to a body part of a human or animal. Plate 2002 can be preferably secured to a body part by adhesive or attachment means. Body part for the purpose of the description includes the body of any living creature including humans and animals of any type as well as birds and other species such as insects. Body 2002 can also include an adhesive surface or any other fastening means, clipping means, and the like which is used to secure body 2002 to an area adjacent to the BTT or on the BTT.
The present invention includes a support structure 2000 removably securable to a body part and having a sensor for measuring biological parameters from a brain tunnel. Any sensor, detector, sensing structure, molecule, moiety, element, radiation detector, a pair of light emitter-detector, fluorescent element, and the like, which can sense, analyze and/or measure an analyte or tissue can be used and disposed in or on measuring portion 2006 or at the end of arm 2004, including contact as well as non-contact detector configurations, and all fall within the scope of the invention. The sensors and/or detectors preferably are positioned on or adjacent to the upper or lower eyelid, and most preferably on or adjacent to the upper eyelid, and even more preferably on or adjacent to an area between the eye and the eyebrow.
Sensing device 2000 preferably comprises: body 2002, which has an inner surface for disposition towards the body part and preferably includes an adhesive surface to securely attach and conform the body 2002 to a body part, and an outer surface for disposition away from the body part; arm 2004 connected to body 2002, said arm 2004 being adjustably positionable and adapted to position sensor 2010 adjacent, on, or firmly against the brain tunnel; and a measuring portion 2006 connected to arm 2004, said measuring portion housing a sensor 2010. Body 2002 is physically conformable to the body part, and preferably includes an outer layer and an inner layer, the inner layer comprised of essentially soft material and including an adhesive surface, said inner layer being attached to an outer layer, said outer layer including a flexible substrate, such as a thin metal sheet, to conform to the body part and to provide stable attachment. A wire is preferably disposed on the outer layer or between the inner layer and the outer layer.
Although sensing device 2000, for purposes of illustration is shown as three parts, it is understood that sensing device 2000 can comprise an integral device fabricated as one piece. Sensing device 2000 can also comprise an integral one-piece device that is fabricated as one piece, but having three different portions. In addition, for example, arm 2004 and measuring portion 2006 can be considered as one piece. Any combination of the parts, namely body, arm, and measuring portion, described herein can be used as the support structure for a sensor, molecule, or detector.
The present invention can employ a cantilever for sensing system 2000, in which arm 2004 is supported rigidly at plate 2002 to carry a load, such as measuring portion 2006, said measuring portion 2006 being disposed along the free end 2026 of said arm 2004. The arm 2004 is fixed at a base of body 2002, with said body 2002 being a support structure exemplarily described in embodiments as a plate; a housing secured to a head mounted gear including a headband, frame of eyewear, hats, helmets, visors, burettes for holding hair; the frame of eyewear or of a head mounted gear, clothing of any type including a shirt, a rigid structure secured to an article of manufacturing such as apparel; and the like. The free end 2026 of arm 2004 is connected to measuring portion 2006 which houses sensor 2010. Accordingly, the sensing device 2000 of the invention has an arm 2004 that distributes force and that can apply force to a body part. One of ways arm 2004 can be positioned and/or apply pressure to a body part is by virtue of a memory shape material of said arm 2004. Any means to apply pressure to a body part can be used in sensing system 2000 including a spring loaded system, in which the spring can be located at the junction 2024 of body 2002 and the arm 2004, or the spring is located at the free end 2026 of arm 2004. It is contemplated that any material with springing capabilities and any other compressible materials and materials with spring and/or compressible capabilities such as foams, sponges, gels, tension rings, high-carbon spring steels, alloy spring steels, stainless steels, copper-base alloys, nickel-base alloys, and the like can be used in sensing device 2000 to apply pressure for better apposition of measuring portion 2006 to the body part. The invention teaches apparatus and methods for creating better apposition and/or applying pressure to a body part or article by any sensor, device, detector, machine, equipment, and the like. Sensor 2010 housed in measuring portion 2006 can therefore apply pressure to a body part, such as the brain temperature tunnel area at the roof of the orbit.
The end of arm 2004 preferably terminates as a bulging part, such as measuring portion 2006, which houses sensor 2010. Arm 2004 can move in relation to plate 2002, thus allowing movement of sensor 2010 housed at the free end 2026 of arm 2004. Although the sensing system 2000 is described for a body part, it is understood that the sensing device 2000 can be applied in an industrial setting or any other setting in which a measurement of an object or article is needed. By way of illustration, sensor 2010 can include a temperature and pressure sensor while the plate 2006 is affixed to a support structure, such as a beam or wall of a machine, and the sensor 2010 is applied against a balloon or a surface, thus providing continuous measurement of the pressure and temperature inside the balloon or surface. Outside surface of body 2002 can include an adhesive surface for securing said body 2002 to a second surface such as a body part or the surface of a machine or any article of manufacturing.
In order to fit with the specialized anatomy and physical configuration of the brain tunnel, specialized sensing devices with special dimensions and configurations are necessary. The preferred dimensions and configurations described herein can be applied to any embodiments of this invention including embodiments described from
The sensing device 2000, as exemplarily illustrated, includes an essentially curved end portion of arm 2004 and an essentially flat remaining portion of arm 2004 said flat portion connected to body 2002. During use arm 2004 is positioned in a curved configuration to fit around the bone of the eyebrow. Arm 2004 has two end portions, namely end portion 2024 which terminates in body 2002 and a free end portion 2026 which terminates in the measuring portion 2006. The preferred length of arm 2004 is equal to or no greater than 15 cm, and preferably equal to or no greater than 8 cm in length, and most preferably equal to or no greater than 5 cm in length. Depending on the size of the person other dimensions of arm 2004 are contemplated, with even more preferable length being equal to or no greater than 4 cm, and for children length equal to or no greater than 3 cm, and for babies or small children the preferred length of arm 2004 is equal to or no greater than 2 cm. Depending on the size of an animal or the support structure being used such as a burette of
The preferred width or diameter of arm 2004 is equal to or no greater than 6 cm, and preferably equal to or no greater than 3 cm, and most preferably equal to or no greater than 1.0 cm. Depending on the size of the person other dimensions for arm 2004 are contemplated, with an even more preferable width or diameter being equal to or no greater than 0.5 cm, and for children width or diameter equal to or no greater than 0.3 cm, and for babies or small children the preferred equal to or no greater than 0.2 cm. Depending on the size of a large person or size of an animal or support structure being used other dimensions for arm 2004 are contemplated, such as width or diameter equal to or no greater than 12 cm.
The preferred height (or thickness) of arm 2004 is equal to or no greater than 2.5 cm, and preferably equal to or no greater than 1.0 cm in thickness, and most preferably equal to or no greater than 0.5 cm in thickness. Depending on the size of the person other dimensions for arm 2004 are contemplated, with even more preferable thickness being equal to or no greater than 0.3 cm, and for children thickness equal to or no greater than 0.2 cm, and for babies or small children the preferred thickness is equal to or no greater than 0.1 cm. Depending on the size of a large person or size of an animal other dimensions for arm 2004 are contemplated, such as thickness equal to or no greater than 3.0 cm.
For devices, in which the preferred configuration of arm 2004 is a cylinder, the preferred diameter of arm 2004 is equal to or no greater than 2.0 cm, and preferably equal to or no greater than 1.0 cm in thickness, and most preferably equal to or no greater than 0.5 cm in thickness. Depending on the size of the person other dimensions for arm 2004 are contemplated, with even more preferable diameter being equal to or no greater than 0.25 cm, and most preferably being equal to or no greater than 0.15 cm, and for children thickness equal to or no greater than 0.2 cm, and for babies or small children the preferred thickness is equal to or no greater than 0.1 cm. Depending on the size of a large person or size of an animal or the structure being used, other dimensions for arm 2004 are contemplated, such as diameter equal to or no greater than 3.0 cm.
The preferred largest dimension of arm 2004 is equal to or no greater than 30 cm, and preferably equal to or no greater than 20 cm, and most preferably equal to or no greater than 10 cm. Preferred dimensions are based on the size of the person or animal and structure being used such as burette, visors, or cap. The preferred length of arm 2004 is no greater than 40 cm, and preferably equal to or no greater than 20 cm, and most preferably equal to or no greater than 10 cm in length. Depending on the size of the person other preferred dimensions for arm 2004 are contemplated, with an even more preferable length being equal to or no greater than 8 cm, and most preferably equal to or no greater than 6 cm, and for adults of small size length equal to or no greater than 5 cm, and for children length equal to or no greater than 4 cm and for babies or small children the preferred length is equal to or no greater than 2 cm. Arm 2004 is preferably curved at its free end 2026 for fitting with the anatomy of the brain tunnel and the facial bone.
The preferred general dimensions for human use by a person of average size for arm 2004 are: height (or thickness or diameter) equal to or less than 0.4 cm, length equal to or less than 6 cm, and width equal to or less than 0.5 cm. The preferred height (or thickness or diameter) of arm 2004 ranges between equal to or more than 0.1 cm and equal to or less than 0.5 cm. The preferred length of arm 2004 ranges between equal to or more than 1.0 cm and equal to or less than 8 cm. The preferred width of arm 2004 ranges between equal to or more than 0.1 cm and equal to or less than 1 cm.
It should be noted that for small animals such as rats, mice, chicken, birds, and other animals using the brain tunnel smaller size and different configurations are contemplated.
In one embodiment the end portions of arm 2004 terminate in plate 2002 and measuring portion 2006. Preferably, arm 2004 is made of a stainless steel type material or aluminum; however, other materials are contemplated, including other metals, plastics, polymers, rubber, wood, ceramic, and the like. The arm 2004 should be sufficiently flexible such that the relative distance between sensor 2010 and a body part may be enlarged or reduced as needed in accordance to the measurement being performed including measurement in which sensor 2010 touches the body part and measurements in which sensor 2010 is spaced away from the body part and does not touch the body part during measurement. An exemplary sensor which does not touch a body part during measurement is a thermopile. Accordingly, measuring portion 2006 can include said thermopile or any radiation detector.
Although
As nanotechnology, MEMS (microelectromechanical systems), and NEMS (nanoelectromechanical systems) progresses other configurations, dimensions, and applications of the present invention are contemplated.
Although
For the purpose of the description thickness and height are used interchangeably. The preferred configuration of sensing device 2000 comprises a body 2002 (including the body of any embodiment from
The preferred configuration of sensing device 2000 comprises a measuring portion 2006 that is thicker than arm 2004. The measuring portion 2006 preferably comprises a bulging portion which is thicker than arm 2004. Arm 2004 is thinner than measuring portion 2006. Arm 2004 has thickness (or height or diameter) which is preferably half or less than the thickness (or height or diameter) of measuring portion 2006. Arm 2004 has thickness (or height or diameter) which is most preferably one third or less than the thickness (or height or diameter) of measuring portion 2006. Even more preferably arm 2004 has thickness (or height or diameter) which is one sixth or less than the thickness (or height or diameter) of measuring portion 2006. It is yet contemplated that for proper functioning in accordance with the size of the user and the principles of the invention, measuring portion 2006 has thickness (or height or diameter) which is 3 times or more larger than the thickness (or height or diameter) of arm 2004.
The preferred configuration of sensing device 2000 comprises an arm 2004 that is longer than the height (or thickness or diameter) of measuring portion 2006. The length of arm 2004 is preferably of larger dimension than the largest dimension of measuring portion 2006. In the exemplary embodiment, measuring portion 2006 is essentially cylindrical, and thus includes a circle, said circle having a diameter. For the purposes of the description, an embodiment in which the circle is replaced by a rectangle, square or other shape, the length of said rectangle, square, or other shape is considered an “equivalent dimension” to the diameter. Accordingly, measuring portion 2006 has diameter (or “equivalent dimension”), which is preferably half or less than the length of arm 2004. Measuring portion 2006 has diameter (or “equivalent dimension”), which is preferably one third or less than the length of arm 2004. It is yet contemplated that for proper functioning in accordance with the principles of the invention, arm 2004 has an even more preferred length, which is 5 times or more greater than the diameter (or “equivalent dimension”) of measuring portion 2006.
The preferred configuration of sensing device 2000 comprises a measuring portion 2006, which is thicker than the body 2002, as illustrated in
The length of body 2002 is preferably of larger dimension than the largest dimension of measuring portion 2006. Preferably, the configuration of sensing device 2000 comprises a body 2002 which has a longer length than the length of measuring portion 2006. When measuring portion 2006 includes a circular configuration, then preferably body 2002 has larger length than the diameter of measuring portion 2006. Measuring portion 2006 has length (or diameter) which is preferably half or less than the length (or diameter) of body 2002. Measuring portion 2006 has length (or diameter) which is preferably one third or less than the length (or diameter) of body 2002. It is yet contemplated that for proper functioning in accordance to the principles of the invention, body 2002 has length (or diameter) which is 4 times or more the length (or diameter) of measuring portion 2006.
The preferred configuration of sensing device 2000 comprises an arm 2004, in which the largest dimension of said arm 2004 is larger than the largest dimension of measuring portion 2006. The preferred configuration of sensing device 2000 comprises a body 2002, in which the largest dimension of said body 2002 is larger than the largest dimension of measuring portion 2006. The preferred configuration of sensing device 2000 comprises an arm 2004, in which the smallest dimension of said arm 2004 is equal to or smaller than the smallest dimension of measuring portion 2006. The preferred configuration of sensing device 2000 comprises a body 2002, illustrated in
It is contemplated that other geometric configurations, besides square, circle, and rectangles, can be used, such as a star, pentagon, octagon, irregular shape, or any geometric shape, and in those embodiments the largest dimension or smallest dimension of the plate 2002 (e.g., body) of sensing device 2000 is measured against the largest dimension or smallest dimension of the other part, such as arm 2004 or measuring portion 2006. The same apply when fabricating sensing device 2000 and the reference is the arm 2004, but now compared to body 2000 and/or measuring portion 2006. Yet the same apply when fabricating sensing device 2000 and the reference is the measuring portion 2006, which is now compared to body 2002 and/or arm 2004. The largest dimension of one part is compared to the largest dimension of the other part. The smallest dimension of one part is compared to the smallest dimension of the other part.
Still in reference to
Sensor 2010 at the end of measuring portion 2006 is connected to processing and display unit 2012 through wire 2014. Wire 2014 has three portions 2060, 2062, 2064. Accordingly, there is seen in
Sensor 2010 at the end 2026 of arm 2004 comprises any sensor or detector, or any element, molecule, moiety, or element capable of measuring a substance or analyzing an analyte or tissue. Exemplary sensor 2010 includes electrochemical, optical, fluorescent, infrared, temperature, glucose sensor, chemical sensor, ultrasound sensing, acoustic sensing, radio sensing, photoacoustic, electrical, biochemical, opto-electronic, or a combination thereof in addition to a light source and detector pair, and the like, all of which for the purpose of the description will be referred herein as sensor 2010.
The preferred largest dimension of sensor 2010 is equal to or no greater than 3 cm, and preferably equal to or no greater than 1.5 cm, and most preferably equal to or no greater than 0.5 cm. Preferred dimensions are based on the size of the person or animal. Depending on the size of the person other dimensions of sensor 2010 are contemplated, such as largest dimension equal to or no greater than 0.3 cm, and for adults of small size dimension equal to or no greater than 0.2 cm, and for small children dimension equal to or no greater than 0.1 cm and for babies preferred dimension is equal to or no greater than 0.05 cm. If more than one sensor is used the dimensions are larger, and if a molecule or moiety are used as sensing element the dimensions are very small and much smaller than any of the above dimensions.
When sensor 2010 comprises a temperature sensor the preferred largest dimension of the sensor is equal to or less than 5 mm, and preferably equal to or less than 4 mm, and most preferably equal to or less than 3 mm, and even more preferably equal to or less than 2 mm. When the temperature sensor has a rectangular configuration, a preferred width is equal to or less than 1 mm, and preferably equal to or less than 500 microns. Those specialized small dimensions are necessary for proper fitting of the sensor with the thermal structure of the tunnel and the entry point of the BTT.
Sensor 2010 can also comprise a radiation source and radiation detector pair, such as a reflectance measuring system, a transmission measuring system, and/or an optoelectronic sensor. Preferably the distance from the outer edge of radiation source (e.g. light emitter) to the outer edge of detector is equal to or less than 3.5 cm, and more preferably equal to or less than 2.0 cm, and most preferably equal to or less than 1.7 cm, and even most preferably equal to or less than 1.2 cm.
In one embodiment sensor system 2010 can further comprise a temperature sensor and include a heating or a cooling element. It is understood that a variety of sensing systems such as optical sensing, fluorescent sensing, electrical sensing, electrochemical sensing, chemical sensing, enzymatic sensing and the like can be housed at the end of arm 2004 or in measuring portion 2006 in accordance to the present invention. Exemplarily, but not by way of limitation, an analyte sensing system such as a glucose sensing system and/or a pulse oximetry sensor comprised of light emitter (also referred to as light source) and light detector can be housed at the end of arm 2004 and operate as sensor system 2010. Likewise a combination light emitter and photodetector diametrically opposed and housed at the end of arm 2004 to detect oxygen saturation, glucose levels, or cholesterol levels by optical means and the like can be used and are within the scope of the present invention. Furthermore, a radiation detector can be housed at the end of arm 2004 for detecting radiation emitted naturally from the brain tunnel and/or the skin area at the brain tunnel between the eye and the eyebrow or at the roof of the orbit.
Sensor 2010 can be a contact or non-contact sensor. In the embodiment pertaining to a contact sensor, exemplarily illustrated as a thermistor, then arm 2004 is positioned in a manner such that sensor 2010 is laying against the skin at the BTT and touching the skin during measurement. When a non-contact sensor is used, two embodiments are disclosed:
measuring portion 2006 is spaced away from the skin and does not touch the skin, and both measuring portion 2006 and sensor 2010 housed in the measuring portion 2006 do not touch the skin during measurement. This embodiment is exemplarily illustrated as an infrared detector. This infrared detector is adapted for receiving infrared radiation naturally emitted form the brain tunnel, between the eye and the eyebrow. Exemplarily infrared radiation emitted includes near-infrared radiation, mid-infrared radiation, and far-infrared radiation. The emitted infrared can contain spectral information and/or radiation signature of analytes, said infrared radiation signature being used for noninvasive measurement of analytes, such as glucose. Alternatively, infrared radiation source, including but not limited to, near-infrared or mid-infrared can be used and the near infrared radiation and/or mid-infrared radiation directed at the brain tunnel generates a reflected radiation from the brain tunnel, which is used for non-invasive measurement of an analyte. In addition, any emitted electromagnetic radiation can contain spectral information and/or radiation signature of analytes, said infrared radiation signature being used for noninvasive measurement of analytes, such as glucose, or analyze of tissue.
sensor 2010 does not touch the skin but walls of a measuring portion 2006, which houses the sensor 2010, touch the skin. In this embodiment, there is a gap or space inside measuring portion 2006 and the skin at the BTT, allowing thus the sensor 2010, which is spaced away from the skin, not to be exposed to air or ambient temperature while still not touching the skin. Accordingly, the sensor 2010 is housed in a confined environment formed by essentially the walls of two structures: the wall of the measuring portion 2006 and the wall formed by the skin at the BTT. This embodiment is exemplarily illustrated as an infrared detector. This infrared detector is adapted for receiving infrared radiation naturally emitted form the brain tunnel. Exemplarily infrared radiation emitted includes near-infrared radiation, mid-infrared radiation, and far-infrared radiation. The emitted infrared can contain the radiation signature of analytes, said infrared radiation signature being used for noninvasive measurement of analytes, such as for example glucose, cholesterol, or ethanol. Alternatively, an infrared radiation source such as near-infrared, mid-infrared, and far-infrared in addition to fluorescent light can be used with said radiation directed at the brain tunnel, which generates a reflected radiation from the brain tunnel, with said reflected radiation containing a radiation signature of an analyte and being used for non-invasive measurement of an analyte. In addition, any source of electromagnetic radiation, any sound generating device, and the like can be housed in a measuring portion.
Sensor 2010 can be covered with epoxi, metal sheet, or other material, and in those embodiments the dimensions in accordance with the invention are the dimension of the material covering sensor 2010.
The preferred largest dimensions for body 2002, illustratively represented by a rectangular plate in
It is understood that plate 2002 can preferably house electronics, microchips, wires, circuits, memory, processors, wireless transmitting systems, light source, buzzer, vibrator, accelerometer, LED, and any other hardware and power source necessary to perform functions according to the present invention. It is also understood that arm 2004 can also house the same hardware as does plate 2002, and preferably houses a LED or lights that are within the field of view of the user, so as to alert the user when necessary. Sensing device 2000 can be powered by a power source housed in the plate 2002. It is understood that sensing device 2000 can be powered by an external power source and that wire 2014 can be connected to said external power source. The external power source can preferably include processing circuit and display.
It is also understood that any support structure, head mounted gear, frame of eyeglasses, headband, and the like can be employed as body 2002, or be coupled to measuring portion 2006, or be connected to arm 2004. When arm 2004 and its sensor 2010 at the end of said arm 2004 is coupled to another support structure, such as frame of eyeglasses, helmet, and the like, the frame of said eyeglasses or said helmet operates as the body 2002, and it is used as the connecting point for arm 2004.
Now in reference to
Body 2020 and connecting portion 2011 can also house electronics, chips, and/or processing circuits. In one embodiment body 2020 includes a soft portion and connecting portion 2011 comprises a hard portion.
For temperature measurement and for monitoring certain biological parameters, measuring portion 2006 preferably includes a non-metallic body 2020, said non-metallic body housing wire portion 2060. In one embodiment for measuring temperature sensor 2010 comprises a temperature sensor and body 2020 preferably comprises insulating material, said insulating material preferably being a soft material and having compressible characteristics. Although compressible characteristics are preferred, it is understood that body 2020 can also comprise rigid characteristics or a combination of rigid and soft portions. Most preferably body 2020 comprises a combination of a rigid part and a soft part, said soft part being located at the free end of body 2020, and which is in contact with a body part, such as of a mammal.
In one embodiment sensor 2010 comprises a pressure sensor or piezoelectric element and operates as a pulse and/or pressure measuring portion. In another embodiment sensor 2010 comprises an electrochemical sensor for measurement of analytes such as glucose. In another embodiment sensor 2010 comprises an ultrasound sensing system. In another embodiment sensor 2010 comprises a photoacoustic sensing system for measurement of chemical substances such as glucose. In another embodiment, sensor 2010 comprises a fluorescent element or fluorescein molecule for evaluating temperature, pressure, pulse, and chemical substances including analytes such as glucose. In another embodiment, sensor 2010 comprises an infrared detector for measuring temperature and/or concentration of chemical substances in blood from radiation naturally emitted from the brain tunnel.
The preferred diameter of measuring portion 2006, illustrated as the diameter of the body 2020, housing a temperature sensor is equal to or no greater than 4 cm, and preferably equal to or no greater than 3 cm, and most preferably equal to or no greater than 2 cm. Depending on the size of the person other even more preferable dimensions for measuring portion 2006 are contemplated, such as diameter equal to or no greater than 1.2 cm, and much more preferably equal to or less than 0.8 cm. For children preferred diameter is equal to or no greater than 0.6 cm, and for babies or small children the preferred diameter is no greater than 0.4 cm. Depending on the size of an animal or person other dimensions for measuring portion 2006 are contemplated, such as diameter equal to or no greater than 5 cm.
When a cylindrical shape is used, the preferred diameter of measuring portion 2006 for chemical or certain physical measurement is no greater than 4 cm, and preferably no greater than 3 cm, and most preferably no greater than 2 cm. The same dimensions apply to a non-cylindrical shape, such as a rectangle, and the preferred length of the rectangle is no greater than 4 cm, and preferably no greater than 3 cm, and most preferably no greater than 2 cm. Depending on the size of the person other even more preferable dimensions for measuring portion 2006 are contemplated, such as a diameter equal to or no greater than 1.2 cm, and much more preferably equal to or no greater than 0.8 cm. For children a preferred diameter is equal to or no greater than 0.7 cm, and for babies or small children the preferred diameter is equal to or no greater than 0.5 cm. Depending on the size of an animal or person other dimensions for measuring portion 2006 are contemplated, such as diameter equal to or no greater than 6 cm.
When a non-cylindrical shape is used, such as a rectangle, the preferred width of measuring portion 2006 is equal to or no greater than 2 cm, and preferably equal to or no greater than 1.5 cm, and most preferably equal to or no greater than 1 cm. Depending on the size of the person other dimensions for measuring portion 2006 are contemplated, such as width equal to or no greater than 0.8 cm and more preferably equal to or no greater than 0.5 cm, and for children width equal to or no greater than 0.4 cm, and for babies or small children the preferred width is equal to or no greater than 0.3 cm. Depending on the size of an animal or person other dimensions for measuring portion 2006 are contemplated, such as width equal to or no greater than 5 cm.
The preferred height (or thickness) of measuring portion 2006, considering a cylindrical shape, is equal to or no greater than 4 cm, and preferably equal to or no greater than 2.0 cm in thickness (or height), and most preferably equal to or no greater than 1.5 cm in thickness (or height), and much more preferably equal to or no greater than 1.3 cm. Depending on the size of the person other dimensions of measuring portion 2006 are contemplated, such as height (or thickness) equal to or no greater than 1.0 cm, and for children thickness (or height), equal to or no greater than 0.8 cm, and for babies or small children equal to or no greater than 0.5 cm. Depending on the size of an animal other dimensions of measuring portion 2006 are contemplated, such as thickness (or height) equal to or no greater than 5 cm. In the case of a measuring portion having a rectangular shape, the thickness or height referred to herein, is replaced by the length of the rectangle, and the above dimensions then are applicable.
The following preferred dimensions in this paragraph pertain to a single sensor, such as a temperature sensor or a pulse sensor or a chemical sensor. In this embodiment the preferred largest dimension of measuring portion 2006 is equal to or no greater than 6 cm, and preferably equal to or no greater than 3 cm, and most preferably equal to or no greater than 1.5 cm. The preferred general dimensions for human use for measuring portion 2006 having a cylindrical shape are height (or thickness) equal to or less than 1.2 cm and diameter equal to or less than 0.8 cm, and most preferably height equal to or less than 1.0 cm and diameter equal to or less than 0.6 cm Preferred length of a non-cylindrical measuring portion 2006 is equal to or less than 1.2 cm and width equal to or less than 0.8 cm, and most preferably length equal to or less than 1.0 cm and width equal to or less than 0.6 cm. The preferred height (or thickness) of measuring portion 2006 ranges between equal to or more than 0.4 cm and equal to or less than 2.0 cm. The preferred diameter of measuring portion 2006 ranges between equal to or more than 0.4 cm and equal to or less than 2.0 cm. Although a temperature sensor was illustrated, it is understood that any sensor can be used. For a pair sensor-detector, a pair light emitter-detector, an infrared sensor, or a sensor and combination with other elements such as a heating element other dimensions can be preferably used, and will be described below.
Measuring portion 2006 can be formed integral with arm 2004 creating a single part consisting of an arm and a measuring portion. Preferably, at least a portion of the material used for measuring portion 2006 is different from the material used for arm 2004. Arm 2004 and measuring portion 2006 preferably comprise two separate parts. In one embodiment for measuring temperature the arm 2004 is made in its majority with an adjustably positionable material such as deformable metal while measuring portion 2006 includes a portion of non-metal materials such as polymers, plastics, and/or compressible materials. The metal portion of arm 2004 can be preferably covered with rubber for comfort. Preferred materials for measuring portion 2006 include foams, rubber, polypropylene, polyurethane, plastics, polymers of all kinds, and the like. Preferably, measuring portion 2006 housing a temperature sensor comprises an insulating material, and includes a compressible material and/or a soft material. Measuring portion 2006 can include any compressible material. Measuring portion 2006 can further include a spring housed in the body 2020. Any other material with spring capabilities can be housed in body 2020 of measuring portion 2006.
Preferably, the end portion 2018 of measuring portion 2006 comprises an insulating material. Preferably the end portion 2018 comprises a non-heat conducting material including non-metallic material or non-metal material. Preferably, the end portion 2018 comprises a soft material including polymers such as polyurethane, polypropylene, Thinsulate, and the like in addition to foam, sponge, rubber, and the like.
The largest dimension of end portion 2018 of measuring portion 2006 is preferably equal to or less than 4 cm, and most preferably equal to or less than 2 cm, and even more preferably equal to or less than 1.5 cm. Accordingly, the dimensions of sensor 2010 preferably follow those dimensions of end portion 2018, said sensor 2010 being of smaller dimension than the dimension of end portion 2018. For the embodiment for measurement of temperature, the largest dimension of end portion 2018 is preferably equal to or less than 1 cm, and most preferably equal to or less than 0.8 cm, and even most preferably equal to or less than 0.6 cm.
Methods and apparatus include measuring portion 2006 touching the body part during measurements or measuring portion 2006 being spaced away from the body part and not touching the body during measurement.
In one preferred embodiment the end portion 2018 of measuring portion 2006 does not have an adhesive surface and the surface around sensor 2010 is also adhesive free. In the prior art, sensors are secured in place by adhesive surfaces, with said adhesive surrounding the sensor. Contrary to the prior art, sensors of the present invention do not have adhesive surrounding said sensors, and said sensors of the present invention are secured in place at the measuring site in the body of a mammal by another structure, such as arm 2004, with the adhesive surface being located away from the sensor surface. Accordingly, in one preferred embodiment of the present invention, the surface of the sensor and the surface of the surrounding material around the sensor is adhesive free.
Now in reference to
To further illustrate the principles of the invention,
Although the preferred embodiment includes an arm 2004 for support structure which works as a sensing device 2000, it is understood that arm 2004 can be replaced by a wire or cord. Accordingly,
Light emitter 2114 preferably emits at least one infrared wavelength and a detector 2118 is adapted to receive and detect at least one infrared wavelength. Light emitter-detector pair 2102 is preferably eccentrically positioned in adhesive patch 2100, said light emitter-detector pair 2102 being located at the edge of patch 2100. Imaginary line from point (A) to point B going across plate 2104 on adhesive patch 2100 housing light emitter-detector pair 2102 measures equal to or less than 3.0 cm, and preferably measures equal to or less than 2.0 cm, and most preferably equal to or less than 1.5 cm. The preferred distance of external edge 2103 of light emitter-detector pair 2102 to the edge 2105 of patch 2100 is less than 14 mm, and preferably less than 10 mm and most preferably less than 5 mm.
Another embodiment includes an adhesive patch housing a sensor comprised of an adhesive surface intersected by a non-adhesive surface. Accordingly, FIG. 86M(1) shows the back side of adhesive patch 2131, said side being disposed toward the skin and in contact with the skin, and comprised of a first adhesive surface 2121, a second non-adhesive surface 2123, and a third adhesive surface 2125 which houses the sensor 2127. The adhesive surface is intersected by a non-adhesive surface. The non-adhesive surface 2123 is adapted to go over the eyebrow, preventing the adhesive from attaching to hair of the eyebrow.
Although a pair radiation emitter-detector has been described, it is understood that another embodiment includes only a radiation detector and the measuring portion 2006 is comprised of a radiation detector for detecting radiation naturally emitted by the brain tunnel. This embodiment can include a infrared detector and is suitable for non-invasive measurement of analytes including glucose as well as temperature, with detector adapted to contact the skin or adapted as non-contact detectors, not contacting skin during measurement.
Preferred diameter at the free end of measuring portion 2150 is equal to or no greater than 3.5 cm, and preferably equal to or no greater than 2.0 cm, and most preferably equal to or no greater than 1.5 cm, and even most preferably equal to or no greater than 1.0 cm. Depending on size of a subject and the type of sensor such as temperature, pressure, and the like the preferred diameter at the free end of measuring portion 2150 is equal to or no greater than 0.8 cm and preferably equal to or no greater than 0.6 cm, and more preferably equal to or no greater than 0.4 cm. Preferred length from point 2150(a) to point 2150(b) of measuring portion 2150 is equal to or no greater than 3 cm, and preferably equal to or no, greater than 1.5 cm, and most preferably equal to or no greater than 1 cm. Depending on size of a subject the preferred length from point 2150(a) to point 2150(b) of cone structure 2150 is equal to or no greater than 0.8 cm and preferably equal to or no greater than 0.6 cm, and more preferably equal to or no greater than 0.4 cm. Measuring portion 2150 can include a contact sensor in which the sensor contacts the skin at the brain tunnel or a non-contact sensor in which the sensor does not contact the skin at the brain tunnel during measurement.
FIG. 86P(1) is an exemplary sensing device 2191 for non-contact measurements at the brain tunnel 2187 and shows sensing portion 2181 housing a sensor illustrated as an infrared sensor 2183 to detect infrared radiation 2185 coming from the brain tunnel 2187. Sensing portion 2181 housing sensor 2183 is connected to body 2193 through adjustably positionable arm 2189. Wire 2195 connects sensor 2183 to body 2193. Sensor 2183 can include any infrared detector, and is adapted to receive and detect infrared radiation from the brain tunnel 2187 for determining temperature, concentration of substances including glucose, and any other measurement of analytes or tissue. Sensor 2183 can also work as a fluorescent sensor, and may include a fluorescent light source or fluorescein molecules. Furthermore, sensor 2183 can include enzymatic sensors or optical sensors.
FIG. 86P(2) is an exemplary sensing device 2197 for non-contact measurements at the brain tunnel 2187 and shows sensing portion 2199 housing a light source-light detector pair assembly 2201, such as an infrared sensor or a fluorescent element. It is contemplated that any electromagnetic radiation including radio waves can be directed at the brain tunnel for determining concentration of analytes and/or presence of analytes and/or absence of analytes and/or evaluating tissue. Light source 2203 directs radiation 2207 such as mid-infrared and/or near-infrared radiation at the brain tunnel 2187 which contains molecules 2205 (including analytes such as glucose), said radiation 2207 generating a reflected radiation that contains the radiation signature of the analyte being measured after said radiation 2207 interacts with the analyte being measured. The reflected radiation 2209 is then detected by detector 2211. The electrical signal generated by the detector 2211 is then fed to a processing circuit (not shown) housed in body 2217 through wire 2213 housed in arm 2215. Sensing portion 2199 housing pair assembly 2201 is preferably connected to body 2217 through an adjustably positionable arm. Detector 2211 can include any infrared detector, and is adapted to receive and detect infrared radiation from the brain tunnel 2187 for determining temperature, concentration of substances including glucose, and any other measurement of analytes or tissue. Detector 2211 can also work as a fluorescent detector for detecting fluorescent light generated.
FIG. 86P(3) is an exemplary hand-held sensing device 2219 for non-contact measurements at the brain tunnel 2187 and shows a light source-light detector pair assembly 2221. Light source 2223 directs radiation 2225 at the brain tunnel 2187 which contains molecules 2205 (including analytes such as glucose), said radiation 2225 generating a reflected radiation 2227 that contains the radiation signature of the analyte being measured after said radiation 2225 interacts with the analyte being measured. The reflected radiation 2227 is then detected by detector 2231. The electrical signal generated by the detector 2231 is then fed to a processing circuit 2233 which calculates the concentration of an analyte based on a calibration reference stored in memory 2235, and display said concentration on display 2237. It is understood that instead of a pair light source-light detector, a stand alone detector for detecting infrared radiation naturally emitted from the brain tunnel can also be used. It is also understood that sensing device 2219 can preferably include a mirror 2229, so as to allow the user to proper position the pair assembly 2221 in line with the skin of the BTT 2187 at the eyelid area. It is contemplated that sensing device 2219 can comprise a mirror in which electronics, display, and pair assembly 2221 are mounted in said mirror, allowing thus measurement of temperature and concentration of analytes being performed any time the user look at the mirror. It is understood that any of the embodiments of the present invention can include a mirror for accurate measurements and proper alignment of a sensor with the BTT.
FIG. 86P(4) is an exemplary sensing device 2239 for non-contact measurements at the brain tunnel 2187, said sensing device 2239 mounted on a support structure 2267, such as a wall or on an article of manufacture or an electronic device including a refrigerator, a television, a microwave, an oven, a cellular phone, a photo camera, video camera, and the like. In this embodiment just performing routine activities such as opening a refrigerator door allows the user to check core temperature, measure glucose, check for cancer markers, and the like. The spectral information contained in the radiation from the brain tunnel is captured by a sensor slidably located on those electronic devices and articles to align with different height individuals. To better align the brain tunnel area 2187 with the sensing device 2239, a light source 2241, such as LED or other confined light source is used. When the eye 2243 of the user is aligned with the light 2241 projecting from a tube or other light path confining or constricting device, the BTT area is aligned with the light source-light detector pair 2251 located at a predetermined distance from the eye. Light source 2253 directs radiation 2255 at the brain tunnel 2187 which contains molecules 2205 (including analytes such as glucose, cholesterol, ethanol, and the like), said radiation 2255 generating a reflected radiation 2257 that contains the radiation signature of the analyte being measured. The reflected radiation 2257 is then detected by detector 2259. The electrical signal generated by the detector 2259 is then fed to a processing circuit 2261 which is operatively coupled with memory 2263, and display 2265. It is understood that an iris scanner, a retinal scanner, or the like or any biometric device such as finger print detectors or camera-like device can be coupled with sensing device 2239. In this embodiment, the pair light source-light detector is preferably replaced by a detector such as for example a thermopile or array of thermopile as previously described in the present invention. Accordingly, light source 2241 can include or be replaced by an iris scanner which identifies a person while measuring the person's core body temperature. This embodiment can be useful at port of entries such as airports in order to prevent entry of people with undetected fever which could lead to entry of fatal disorders such as SARS, bird flu, influenza, and others. The temperature of the person, measured by the sensor aimed at the BTT, is coupled to the identity of the person acquired through the iris scanning, with said data temperature-iris scan being stored in a memory. The system may include a digital camera, allowing a picture of the person being coupled with the body core temperature and the iris scan. A processor identifies whether the temperature is out of range, and activates an alarm when fever is detected. The system allows measurement of temperature and concentration of analytes being performed any time the user look at the iris scanner.
It is understood that a sensor for detecting radiation or capturing a signal from the brain tunnel can be mounted on any device or article of manufacturing. Accordingly and by way of further illustration, FIG. 86P(5) shows a sensing device 2273 including a sensor 2269 mounted on a web-camera 2271 which is secured to a computer 2275 for measurements of radiation from the brain tunnel 2187, said sensing device 2273 having a cord 2277 which is connected to computer 2275 and carries an electrical signal generated by detector 2269, with the electrical signal being fed into the computer 2275. In this embodiment, the processor, display and other electronics are housed in the computer. Any time a user looks at the web-camera, measurement of body temperature and/or determination of concentration of analyte can be accomplished.
Measuring portion 2006 has an essentially circular configuration and has a wire portion 2166 disposed in the internal part 2164. External part 2162 can comprise a washer or ring around internal part 2164. Internal part 2164 has preferably a cylindrical shape and houses wire portion 2166 inside its structure and houses sensor 2170 at its free end. Wire portion 2166 terminates in wire portion 2167 secured to arm 2161. Although a circular configuration is shown, any other shape or combination of shapes is contemplated.
FIG. 86Q(1) is a perspective diagrammatic view of measuring portion 2006 of
Part 2164 has preferably an essentially cylindrical configuration, although any other configuration or geometry is contemplated and can be used in accordance with the invention. The preferred diameter of part 2164 is equal to or no greater than 3.0 cm, and preferably equal to or no greater than 2.0 cm in diameter or length, and most preferably equal to or no greater than 1.0 cm. For a non-circular configuration that includes a width, the preferred width of part 2164 is equal to or no greater than 3.0 cm, and preferably equal to or no greater than 1.5 cm in width, and most preferably equal to or no greater than 1.0 cm in width. The preferred height (or thickness) of part 2164 is equal to or no greater than 3.5 cm, and preferably equal to or no greater than 2.5 cm, and most preferably equal to or no greater than 1.0 cm, and much more preferably equal to or no greater than 0.7 cm. The preferred largest dimension of part 2164 is no greater than 3.5 cm, and preferably no greater than 2.0 cm in diameter or length, and most preferably no greater than 1.5 cm.
For temperature monitoring, preferably, part 2162 and part 2164 are made with an insulating material such as polyurethane, polypropylene, thinsulate, and the like, however, other materials are contemplated, including other polymers, foams, and the like. Part 2162 and part 2164 preferably comprise a compressible material for certain applications.
Rigid portion 2281 of plate 2180 continues as arm 2184, said arm 2184 having a free end 2188 which connects to measuring portion 2186. Measuring portion 2186 includes sensor 2190, said sensor 2190 is preferably disposed as a bulging portion. During use the method includes the steps of, applying plate 2180 to the skin, bending arm 2184 to fit with the particular anatomy of the user and for positioning the sensor 2190 on or adjacent to the skin of the BTT or other tunnels of the invention. Other steps include measuring an analyte or analyzing a tissue, producing a signal corresponding to the measurement and analysis, and reporting the results. Further steps can include processing the signal and displaying the result in alphanumerical format, audible format, a combination thereof and the like. A further step can include transmitting the signal to another device using a wireless or wired transmitter. The step of chemical measuring an analyte can be replaced by measuring a physical parameter such as temperature, pulse, or pressure.
FIG. 86R(1) shows a schematic view of sensing device 2289 when worn by a user 2293 and including a headband 2283 around the forehead, said headband 2283 attached to plate 2291, said plate 2291 having arm 2285 and a sensor 2287 which receives radiation from the brain tunnel 2187.
FIG. 86R(2) shows a schematic view of sensing device 2295 having a swivel mechanism 2297 at the junction of arm 2299 and body 2301, said swivel mechanism allowing rotation and motion of arm 2299 (represented by broken arrows) for positioning sensor 2303 on or adjacent to a brain tunnel. Sensor 2303 is illustrated as a light source-detector pair, with wire 2305 connecting said sensor 2303 to a processing and display unit 2307.
FIG. 86R(3) shows the embodiment of FIG. 86R(2) when worn by a user 2309, and depicting light source-detector pair 2303 positioned on the brain tunnel 2187. Body 2301 is secured to the forehead 2311 preferably by adhesive means 2313 disposed at the inner surface of body 2301, said body 2301 connected to arm 2299 by swivel mechanism 2297, which is preferably positioned over the eyebrow.
FIG. 86S(1) shows a side view of sensing device 2000 including wire 2198 which is disposed flat and without any bending, and runs from sensor 2210 in measuring portion 2196 to body 2192. Measuring portion 2196 is aligned with arm 2194 and body 2192. In this embodiment, the axis of measuring portion 2196 is in line with arm 2194, and forms a 180 degree angle. During fabrication the 180 degree angle configuration and flat shape is obtained. During use, in accordance with the method of the invention, the arm 2194 is bent. Since arm 2194 is flexible and adjustably positionable, during use arm 2194 is bent for positioning measuring portion 2196 in line with the brain tunnel.
Accordingly, FIG. 86S(2) shows sensing device 2000 worn by a user with arm 2194 bent in order to position sensor 2210 of measuring portion 2196 on or adjacent to brain tunnel area 2214 between the eyebrow 2212 and eye 2216. Wire 2198 connects sensor 2210 to body 2192, said body 2192 being preferably secured to the forehead.
Sensing device 2000 can be powered by active power including batteries secured to body 2002, solar power, or by wires connecting sensing device 2000 to a processing unit. It is also understood that any of the sensors housed in an adhesive patch or housed in support structure 2000 can operate on a passive basis, in which no power source is housed in said sensor system. In the case of passive systems, power can be provided remotely by electromagnetic waves. An exemplary embodiment includes Radio Frequency ID methodology, in which a nurse activates remotely the patch or sensor system 2000 of the present invention which then reports back the identification of the patient with the temperature being measured at the time of activation. The sensor system can also include a transponder which is powered remotely by a second device, which emits a radio signal or any suitable electromagnetic wave to power the sensor system. Besides temperature, any other biological parameter can be measured such as pulse, blood pressure, levels of chemical substances such as glucose, cholesterol, and the like in addition to blood gases, oxygen levels, oxygen saturation, and the like.
It is yet understood that arm 2004 connected to measuring portion 2006 can be detachably connected to plate 2002, with said arm 2004 and measuring portion 2006 becoming a disposable part while plate 2002, which preferably houses expensive wireless transmitter and other electronics and power source, works as the durable part of the device 2000. It is also understood that measuring portion 2006 can be detachably connected to arm 2004, said measuring portion 2006 being disposable. It is yet understood that the free end of measuring portion 2006 can be connected to a wire inside body 2020 of measuring portion 2006, said free end housing sensor 2010 being the disposable part. It is also contemplated that the present invention is directed to a method and apparatus in which the disposable part is the body 2002 and the durable reusable part is the measuring portion 2006 and arm 2004. In this embodiment an expensive sensor such as an infrared detector can be disposed in the measuring portion 2006, and is detachably connected to plate 2002, said sensor being the reusable part while the body 2002 being the disposable part. Accordingly, FIG. 86T(1) shows sensing device 2000 including arm 2004, measuring portion 2006 with sensor 2010, and plate 2002, said plate 2002 housing a circuit board 2200 including a processor 2222 operatively coupled to a memory 2228, power source 2224, and transmitter 2226. Wire 2220 connects sensor 2010 to circuit board 2200.
FIG. 86T(2) shows an exemplary embodiment of sensing device 2000 comprised of two separable pieces including a durable part 2230, represent by the body, and a disposable part 2232, represented by the arm and measuring portion. It is understood that sensing device can comprise one or more parts and a combination of durable and disposable parts. Accordingly, in FIG. 86T(2) there is seen durable part 2230 represented by plate 2002, said plate 2002 having a circuit board 2200 including processor 2222 operatively coupled to a memory 2228, power source 2224, and transmitter 2226. Disposable part 2232 comprises arm 2204 and measuring portion 2006. Plate 2002 has an electrical connector 2234 which is electrically and detachably connected to an electrical connector 2236 of arm 2004, preferably creating a male-female interface for electrical connection in which wire 2220 of arm 2004 ends as a male connector 2236 adapted to connect to a female connector 2234 of plate 2002.
FIG. 86T(3) shows an exemplary embodiment of sensing device 2000 comprised of two separable pieces including a durable part 2240 further comprised of arm 2004 and plate 2002 and a disposable part 2242 comprised of measuring portion 2006, said measuring portion 2006 including a light emitter-light detector pair 2244. Arm 2004 has an electrical connector 2246 which is electrically and detachably connected to an electrical connector 2248 of measuring portion 2006.
It is contemplated that durable part represented by plate 2002 can comprise power source and a LED for alerting changes in the biological parameter being measured or to identify that the useful life of the device has expired. Plate 2002 can also house a power source and a wireless transmitter, or a power source and a display for numerical display, or/and a combination thereof. Alternatively plate 2002 works as a passive device and comprises an antenna and other parts for electromagnetic interaction with a remote power source. Another embodiment includes a passive device or an active device comprised of a patch having a sensor and a LED, said LED being activated when certain values are detected by the sensor, allowing a nurse to identify for example a patient with fever by observing a patch in which the LED is on or flashing.
Any biological parameter and tissue can be measured and/or analyzed at the brain tunnel including temperature, concentration of chemical substances, blood pressure, pulse, and the like. Exemplarily a blood gas analyzer and a chemical analyzer will be described. The embodiment relates to a device for the transcutaneous electrochemical or optical determination of the partial pressure of oxygen and/or analytes in the blood of humans or animals at the Brain Temperature Tunnel (BTT) site, also referred to as brain tunnel (BT). The invention comprises a measuring portion 2006 which includes a measuring cell having electrodes, said cell having a surface which is to be disposed in contact with the skin at the BTT. The cell in measuring portion 2006 can include a heating or a cooling element for changing the temperature of the brain tunnel. Preferably the measuring portion 2006 includes an electrical heating element. Besides contacting the skin, the measuring surface of measuring portion 2006 can be spaced away from the skin at the brain tunnel for measuring analytes and the partial pressure of oxygen.
For measurement of oxygen the measuring portion 2006 preferably includes a Clark type sensor, but it is understood that any electrochemical or optical system can be used in accordance with the present invention and fall within the scope of the present invention. Various sensors, electrodes, devices including polarygraphic sensors, enzymatic sensors, fluorescent sensors, optical sensors, molecular imprint, radiation detectors, photodetectors, and the like can be used.
In one preferred embodiment, the measuring portion 2006 includes an element to increase blood flow, such as by way of illustration, a heating element, a suctioning element, or fluid that increases permeability of skin. Preferably a heating element is provided, whereby the sensing surface (or measuring surface) of the measuring portion 2006 is adapted to increase the temperature of the skin at the brain tunnel. This heating element increases blood flow to the entrance of the BT and accelerates the oxygen diffusion through the skin at the BT. The measuring portion 2006 is preferably located in apposition to the BT zone associated with the arterial supply and the orbital artery or any of the arterial branches located in the BT area, in order to achieve ideal measurement of the arterial oxygen and the arterial partial oxygen pressure. The transcutaneously measured oxygen pressure on the skin at the entrance of the BT is obtained by placing a specialized measuring portion 2006 of special geometry and dimensions on the skin at the BTT, in accordance with the present invention and the specialized dimensions and shape of the sensor and support structures as described herein.
In arterial blood an equilibrium exists between the percentage of oxidized hemoglobin and the partial oxygen pressure. When the blood is heated, this equilibrium is shifted so that the partial oxygen pressure increases. Therefore, when the BT method is used, the partial oxygen pressure in the peripheral blood vessels in the BT is higher than in the arteries. The oxygen coming from the arterial region of the BT diffuses through the skin at the BTT.
With exception of the skin at the BT, the skin cells in the whole body consume oxygen during diffusion of oxygen through the skin, because said skin is thick and has a thick underlying layer of subcutaneous tissue (fat tissue). Thus, the oxygen pressure at the area of the epidermis in all areas of the body, with exception of the BT area, is much lower than the actual oxygen pressure in the peripheral blood vessels. However, in the specialized skin areas of the BT the oxygen levels remain stable since the skin at the BT is the thinnest skin in the whole body and free of adipose (fat) tissue.
The specialized skin area of the BT between the eyebrow and the eye, at the roof of the orbit shown in
Since consumption of oxygen is proportional to the thickness of the skin and of subcutaneous tissue (which contains the fat tissue), and further considering that the BT, as described above and surrounding physio-anatomic tunnels disclosed in the present invention have very thin skin and no subcutaneous tissue, the amount of oxygen at the epidermis (skin) at the entrance of said tunnels is not reduced, and remains proportional to the amount present in the peripheral blood vessels. Thus, the amount of gases such as oxygen, carbon dioxide, and other gases as well as analytes present in the skin of the BTT is proportional to the amount present in blood.
Another advantage of the present invention is that the heating element does not need to reach high levels of temperature, such as 44 degrees C., since the tunnel area is extremely vascularized and associated with a unique blood vessel which is terminal (which means that the total amount of blood is delivered to the site) in addition to having the thinnest skin interface in the whole body, thereby allowing a lower temperature of a heating element to be used for increasing blood flow to the area. The preferred temperature of the heating element is equal to or less than 44 degrees Celsius, and preferably equal to or less than 41 degrees Celsius, and most preferably equal to or less than 39 degrees Celsius, and even most preferably equal to or less than 38 degrees Celsius.
The electrochemical sensor of the measuring portion 2006 for blood gas and glucose analysis has the same specialized dimensions and shape described for the other sensors of the invention, in accordance with the present invention and specialized anatomy of the BT and other surrounding tunnels. The device includes a measuring portion 2006 having a sensor, said sensor preferably being an electrochemical or optical sensor, and an associated heating element of specialized dimensions, with said measuring portion 2006 located adjacent to the BT or on the skin at the BT or other described tunnels of the invention. One of the objects of the invention includes providing a device of the described kind to be used at the BT for measurement of the arterial oxygen pressure and other blood gases such as carbon dioxide, carbon monoxide, anesthetic gases, and the like.
Skin 2270 of the prior art is thick and has a thick subcutaneous layer 2272 in comparison with the thin skin 2290 of the BT. In the method of the prior art, oxygen molecules 2280 from small blood vessel 2278, which is located deep in the body, have to cross thick layers of skin 21742 (fat tissue), 2174 (dermis), 2176 (epidermis and dead cells) present in said skin 2270 in order for said oxygen molecules 2280 to reach a conventional sensor of the prior art. Accordingly, in the method of the prior art the oxygen 2280 from vessel 2278 has a long path before reaching a sensor of the prior art. Oxygen 2280 diffuses through the wall of the small blood vessel 2278 and through the subcutaneous tissue 2272 to finally reach a thick dermis 2274 and a thick layer of dead cells 2276 at skin 2270, to only then reach conventional sensors of the prior art. As can be seen, the number of oxygen molecules 2280 drop drastically from around vessel 2278 to surface of skin 2271 as it moves along the long path of conventional thick skin 2270 present in the body.
Contrary to the prior art, the method and device of the present invention uses a specialized and extremely thin skin 2290 of the BT, in which oxygen molecules 2280 from vessel 2284 have an extremely short path to reach specialized sensor 2000 of the present invention. Oxygen molecule 2280 is right underneath the thin skin 2290 since terminal large vascular area 2284 lies just underneath the thin skin 2290, and thus oxygen 2280 rapidly and in an undisturbed fashion reaches specialized sensor 2000. This allows an undisturbed diffusion of oxygen from vessel 2284 to sensor 2000 without any drop of the partial oxygen pressure. Because the specialized skin 2290 of the BT produces a rapid and undisturbed diffusion of oxygen (and other blood gases) to the special sensor 2000 of the present invention and the area measured is characterized by a natural condition of hyperperfusion, the present invention results in more accurate measurement than previously available estimates of partial blood gas pressures.
An exemplary transcutaneous blood gas sensor of the present invention consists of a combined platinum and silver electrode covered by an oxygen-permeable hydrophobic membrane, with a reservoir of phosphate buffer and potassium chloride trapped inside the electrode.
In reference to
The skin 2290 at the BT 2282 is heated by heating source 2298 adjacent to the area of sensor 2292 with consequent increase in arterial blood flow. Electrodes and a voltage source in processing circuit 2302 provide a circuit in which the electrical current flow is dependent on the partial oxygen pressure at the sensor 2292.
Although a contact device and method was illustratively shown, it is understood that a non-contact method and device can be equally used in accordance with the invention. It is also understood that a variety of support structures, disclosed in the present invention, can be used for housing the elements of measuring portion 2006 including adhesive patches, head mounted gear such as eyewear and headbands, and the like. In addition to or as a substitute of wired transmission, the transmission of the signal can use a wireless transmitter and the sensor system of the invention can include a wireless transmitter.
Since the skin at the BT is highly oxygenated and has a high blood flow, the heating element or any element to cause increase blood flow is not necessary in most patients. Accordingly, another preferred embodiment of the present invention is shown in
The device of the present invention is adapted to measure any component present in the blood by utilizing a plurality of sensors adjacent to or in apposition to the skin of the BT and other physiologic and anatomic tunnels of the present invention. It is understood that an electrochemical sensor or optical sensor can be used to measure other blood components such as glucose, carbon dioxide, cholesterol, pH, electrolytes, lactate, hemoglobin, and any of the blood components.
The sensor system of the invention includes skin surface oxygen pressure measurement, carbon dioxide pressure measurement and measurement of the arterial partial pressure of oxygen or carbon dioxide by locally applying a specialized device on the skin at the BTT comprised by the various new and specialized supports structures. A processing circuit uses the skin surface oxygen or carbon dioxide pressure at the BTT and other tunnels of the invention to calculate the arterial partial pressure of oxygen or carbon dioxide. The processing circuit can be operatively coupled to a memory for correlating the acquired value with a stored value. A processing circuit can be further coupled to a display for visual or audible reporting of the values.
The present invention also discloses a method comprising the steps of applying a electrochemical sensor or an optical sensor or a radiation detector on or adjacent to the skin at the entrance of the BT and other tunnels, applying electrical energy, and measuring at least one analyte including at least one of glucose, oxygen, cholesterol, oxygen, and carbon dioxide. An alternative step includes increasing blood flow to the area by using at least one of heating, creating suction, mechanically tapping the area, using sound waves such as ultrasound, increasing BT skin permeability with laser light, increasing BT skin permeability with chemical substances, and the like.
Sensor 2358 can also work as an infrared detector for measurement of analytes such as glucose. Likewise sensor 2358 can operate as a light emitter-detector pair for measuring analytes. The noninvasive measurement methods of the present invention takes advantage that the BT is an ideal emitter of infrared radiation at precisely the right spectral radiation for measuring substances such as glucose. The emission from the BT works as a black body emission. The emission from the BT contains the radiation signature of analytes. Contrary to other parts of the body in which radiation is deep inside the body, the radiation at the BT is the closest to the surface of the body. A variety of cooling or heating elements can be incorporated to enhance measurement of glucose at the BT. Besides mid-infrared radiation, it is also understood that near-infrared spectroscopy can be used of the measurement of glucose at the BTT. It is also understood that mid-infrared spectroscopy can be used of the measurement of glucose at the BTT. It is also understood that far-infrared spectroscopy can be used of the measurement of glucose at the BTT.
Furthermore, techniques such as Raman spectroscopy can also be used for measuring the concentrations of blood analytes at the BTT and other tunnels of the present invention. Raman spectroscopy has sharp spectral features, which are characteristic for each molecule. This strength is ideally suited to blood analyte measurements, where there are many interfering spectra, many of which are much stronger that that of blood analytes. Accordingly, in the present invention Raman light is generated in the tissue at the BT and collected by a mirror secured to any of the support structures of the present invention such as the frame of eyeglasses, clips, adhesive patches attached to the skin, finger like structure with a plate and an arm, and the like. A fiber bundle in any of the support structures of the present invention guides the collected Raman light to a portable spectrograph and/or to a processor and a CCD. Since there are no interfering elements at the BT, the Raman's sharp spectral features enable accurate detection of blood analyte spectra including glucose, urea, triglyceride, total protein, albumin, hemoglobin and hematocrit.
A light source can illuminate the skin at the brain tunnel area and generate a detectable Raman spectrum for detecting analytes based on said spectrum. Accordingly, another embodiment of the present invention includes an apparatus and method for the non-invasive determination of an analyte comprising a light source for generating an excitation light directed into the brain tunnel and an optical system coupled with said excitation light, said optical system configured for directing the excitation light into the brain tunnel to generate a detectable Raman spectrum thereof, a light detector coupled with said optical system and configured to detect a Raman spectrum from the brain tunnel, a processor operatively coupled with said detector said processor including a processing circuit, said processing circuit having a computer readable medium having code for a computer readable program embodied therein for comparing Raman spectrum from the brain tunnel to a reference radiation corresponding to the concentration of an analyte, and a memory operatively coupled with said processor. The electrical signal corresponding to Raman spectrum from the brain tunnel is fed into the processing circuit and compared to Raman spectrum from the brain tunnel corresponding to the analyte concentration stored in the memory.
It is also understood that glucose at the BTT can be measured with enzymatic sensors such as glucose oxidase as well as artificial glucose receptors. Fluorescence techniques can also be used and include use of engineered molecules, which exhibit altered fluorescence intensity or spectral characteristics upon binding glucose, or use of competitive binding assays that employ two fluorescent molecules in the fluorescent resonance energy transfer technique. In addition, “reverse iontophoresis”, with a device held in the specialized support structures of the invention such as eyeglasses can be used, and interstitial fluid from the BT area removed for analysis. Ultrasound applied to the BT and/or a low-level electrical current on the skin of the BT, by convective transport (electro-osmosis) can also be used for moving glucose across the thin skin of the BT and other tunnels around the eye. In addition, light scattering and photoacoustic spectroscopy can be used to measure various substances such as glucose. Pulsed infrared light directed at the BT, when absorbed by molecules, produces detectable ultrasound waves from the BT, the intensity and patterns of which can be used to measure glucose levels. The apparatus and methods of the present invention then determines the concentration of an analyte using a processor that correlates signals from the brain tunnel with a reference table, said reference table having values of analytes corresponding to signals from the brain tunnel.
Furthermore, a detector having an ultrasound and a light source illuminates the skin at the rain tunnel area with a wavelength that is absorbed by the analyte being measured and generates a detectable ultrasound wave from the brain tunnel for detecting analytes based on said ultrasound wave and light absorption. Accordingly, another embodiment of the present invention includes an apparatus and method for the non-invasive determination of an analyte comprising a light source for generating light directed into the brain tunnel and an ultrasound configured to waves generated from the brain tunnel, a processor operatively coupled with said ultrasound said processor including a processing circuit, said processing circuit having a computer readable medium having code for a computer readable program embodied therein for comparing absorption of radiation from the brain tunnel based on the signal from the ultrasound to a reference radiation corresponding to the concentration of an analyte, and a memory operatively coupled with said processor. The electrical signal corresponding to the intensity of sound waves is used to determine radiation absorption of light from the brain tunnel, which is used to determine the concentration of the analyte, said signal being fed to the processing circuit and compared with the radiation absorption from the brain tunnel corresponding to the analyte concentration stored in the memory.
The present invention includes non-invasive optical methods and devices for measuring the concentration of an analyte present in the BT. A variety of optical approaches including infrared spectroscopy, fluorescent spectroscopy, and visible light can be used in the present invention to perform the measurements in the BT including transmission, reflectance, scattering measurement, frequency domain, or for example phase shift of modulated light transmitted through the substance of interest or reflected from the BT, or a combination thereof.
The present invention includes utilizing the radiation signature of the natural black-body radiation emission from the brain tunnel. Natural spectral emissions of infrared radiation from the BT and vessels of the BT include spectral information of blood components such as glucose. The radiation emitted by the BT as heat can be used as the source of infrared energy that can be correlated with the identification and measurement of the concentration of the substance of interest. Infrared emission in the BT traverses only an extremely small distance from the BT to the sensor which means no attenuation by interfering constituents. The devices and methods can include direct contact of the instrument with the skin surface at the BT or the devices of the invention can be spaced away from the BT during the measurements.
The methods, apparatus, and systems of the present invention can use spectroscopic analysis of the radiation from the BT to determine the concentration of chemical substances present in such BT while removing or reducing all actual or potential sources of errors, sources of interference, variability, and artifacts. The natural spectral emission from the BT changes according to the presence and concentration of a substance of interest. One of the methods and apparatus involves using a radiation source to direct electromagnetic radiation at the BT with said radiation interacting with the substance of interest and being collected by a detector. Another method and apparatus involves receiving electromagnetic radiation naturally emitted from the BT with said radiation interacting with the substance of interest and being collected by a detector. The data collected is then processed for obtaining a value indicative of the concentration of the substance of interest.
The infrared thermal radiation emitted from the brain tunnel follow Planck's Law, which can be used for determining the concentration of chemical substances. One embodiment includes determining the radiation signature of the substance being measured to calculate the concentration of the substance. Another embodiment includes using a reference intensity calculated by measuring thermal energy absorption outside the substance of interest band. The thermal energy absorption in the band of substance of interest can be determined via spectroscopic means by comparing the measured and predicted values at the BT. The signal is then converted to concentration of the substance of interest according to the amount of infrared energy absorbed.
The apparatus uses the steps of producing output electrical signals representative of the intensity of the radiation signature and sending the signal to a processor. The processor is adapted to provide the necessary analysis of the signal to determine the concentration of the substance of interest and is coupled to a display for displaying the concentration of the substance of interest, also referred to herein as analyte.
The analyte measured or detected can be any molecule, marker, compound, or substance that has a radiation signature. The radiation signature preferably includes a radiation signature in the infrared wavelength range including near-infrared, mid-infrared, and far-infrared. The analyte being measured can preferably have a radiation signature in the mid-infrared range or the near infrared range.
Infrared spectroscopy, as used in some embodiments of the present invention, is a technique based on the absorption of infrared radiation by substances with the identification of said substances according to its unique molecular oscillatory pattern depicted as specific resonance absorption peaks in the infrared region of the electromagnetic spectrum. Each chemical substance absorbs infrared radiation in a unique manner and has its own unique absorption spectra depending on its atomic and molecular arrangement and vibrational and rotational oscillatory pattern. This unique absorption spectra allows each chemical substance to basically have its own infrared spectrum, also referred as fingerprint or radiation signature which can be used to identify each of such substances.
In one embodiment radiation containing various infrared wavelengths is emitted at the substance or constituent to be measured, referred to herein as “substance of interest”, in order to identify and quantify said substance according to its absorption spectra. The amount of absorption of radiation is dependent upon the concentration of said chemical substance being measured according to Beer-Lambert's Law.
One embodiment includes a method and apparatus for analyte measurement, such as blood glucose measurement, in the near infrared wavelength region between 750 and 3000 nm and preferably in the region where the highest absorption peaks are known to occur, such as the radiation absorption signature of the substance being measured. For glucose, for example, the near infrared region includes the region between 2080 to 2200 nm and for cholesterol the radiation signature is centered around 2300 nm. The spectral region can also include visible wavelength to detect other chemical substances including glucose or cholesterol.
The apparatus includes at least one radiation source from infrared to visible light which interacts with the substance of interest and is collected by a detector. The number and value of the interrogation wavelengths from the radiation source depends upon the chemical substance being measured and the degree of accuracy required. As the present invention provides reduction or elimination of sources of interference and errors, it is possible to reduce the number of wavelengths without sacrificing accuracy. Previously, the mid-infrared region has not been considered viable for measurement of analytes in humans because of the presence of fat tissue and the high water absorption that reduces penetration depths to microns. The present invention can use this mid-infrared region since the blood with the substance of interest is located very superficially in an area void of fat tissue which allows sufficient penetration of radiation to measure said substance of interest.
The present invention reduces variability due to tissue structure, interfering constituents, and noise contribution to the signal of the substance of interest, ultimately substantially reducing the number of variables and the complexity of data analysis, either by empirical or physical methods. The empirical methods including Partial Least Squares (PLS), principal component analysis, artificial neural networks, and the like while physical methods include chemometric techniques, mathematical models, and the like. Furthermore, algorithms were developed using in-vitro data which does not have extraneous tissue and interfering substances completely accounted for as occurs with measurement in deep tissues or with excess background noise such as in the skin with fat tissue. Conversely, standard algorithms for in-vitro testing correlates to the in vivo testing of the present invention since the structures of the brain tunnel approximates a Lambertian surface and the skin at the brain tunnel is a homogeneous structure that can fit with the light-transmission and light-scattering condition characterized by Beer-Lambert's law.
Spectral radiation of infrared energy from the brain tunnel can correspond to spectral information of the substance of interest or analyte. These thermal emissions irradiated as heat at 38 degrees Celsius can include the 3,000 nm to 30,000 nm wavelength range, and more precisely the 4,000 nm to 14,000 nm range. For example, glucose strongly absorbs light around the 9,400 nm band, which corresponds to the radiation signature of glucose. When mid-infrared heat radiation is emitted by the brain tunnel, glucose will absorb part of the radiation corresponding to its band of absorption. Absorption of the thermal energy by glucose bands is related in a linear fashion to blood glucose concentration in the brain tunnel.
The infrared radiation emitted by the BTT contains the radiation signature of the substance being measured and the determination of the analyte concentration is done by correlating the spectral characteristics of the infrared radiation emitted from the brain tunnel to the analyte concentration for that radiation signature. The analyte concentration can be calculated from the detected intensity of the infrared radiation signature, said radiation signature generating an electrical signal by a detector, with said signal being fed into a microprocessor. The microprocessor can be coupled to a memory which stores the concentration of the analyte according to the intensity of the radiation signature of the analyte being measured. The processor calculates the concentration of the substance based on the stored value in the memory. The processor is operatively coupled with said detector, said processor including a processing circuit, said processing circuit having a computer readable medium having code for a computer readable program embodied therein for comparing infrared spectrum from the brain tunnel to a reference radiation corresponding to the concentration of an analyte, and a memory operatively coupled with said processor. The electrical signal corresponding to the infrared spectrum from the brain tunnel is fed into the processing circuit and compared to infrared spectrum from the brain tunnel corresponding to the analyte concentration stored in the memory. The infrared spectrum preferably includes near-infrared or mid-infrared radiation.
One embodiment includes a device and method for measuring an analyte concentration in the blood or tissue of the BT. One embodiment includes detecting the level of infrared radiation naturally emitted from the BT. One embodiment includes detecting the level of infrared radiation emitted from the BT after directing radiation at the BTT.
One embodiment includes a device which measures the level of mid-infrared radiation from the surface of a brain tunnel and determines the concentration of an analyte based on the analyte's infrared radiation signature. The radiation signature can be preferably in the infrared region of the spectrum including near-infrared or mid-infrared. The device can include a filter, a detector, a microprocessor and a display.
A detector having a light source can illuminate the skin at the brain tunnel area and generate a detectable infrared radiation for detecting analytes based on said infrared spectrum. The detectable infrared radiation from the brain tunnel contains the radiation signature of the analyte being measured. Accordingly, another embodiment of the present invention includes an apparatus and method for the non-invasive determination of an analyte comprising a light source for generating an infrared light directed into the brain tunnel and an infrared radiation detector configured to detect infrared radiation from the brain tunnel, a processor operatively coupled with said detector, said processor including a processing circuit, said processing circuit having a computer readable medium having code for a computer readable program embodied therein for comparing infrared radiation from the brain tunnel to a reference radiation corresponding to the concentration of an analyte, and a memory operatively coupled with said processor. The electrical signal corresponding to infrared radiation signature from the brain tunnel is fed into the processing circuit and compared to infrared radiation signature from the brain tunnel corresponding to the analyte concentration stored in the memory.
A variety of radiation sources can be used in the present invention including LEDs with or without a spectral filter, a variety of lasers including diode lasers, a Nernst glower broad band light emitting diode, narrow band light emitting diodes, NiChrome wire, halogen lights a Globar, and white light sources having maximum output power in the infrared region with or without a filter, and the like. The radiation sources have preferably enough power and wavelengths required for the measurements and a high spectral correlation with the substance of interest. The range of wavelengths chosen preferably corresponds to a known range and includes the band of absorption for the substance of interest or radiation signature of the substance. The instrument comprises a light source which may be any suitable infrared light source, including mid-infrared light source, near-infrared light source, far-infrared light source, fluorescent light source, visible light source, radio waves, and the like.
A light source can provide the bandwidth of interest with said light being directed at the substance of interest in the brain tunnel. A variety of filters can be used to selectively pass one or more wavelengths which highly correlate with the substance of interest. The filter can select the wavelength and includes bandpass filter, interference filter, absorption filter, monochromator, grating monochromator, prism monochromator, linear variable filter, circular variable filter, acousto-optic tunable filter, prism, and any wavelength dispersing device
The radiation can be directly emitted from a light source and directly collected by a photodetector, or the radiation can be delivered and collected using optic fiber cables. An interface lens system can be used to convert the rays to spatial parallel rays, such as from an incident divergent beam to a spatially parallel beam.
The detector can include a liquid nitrogen cooled detector, a semiconductor photodiode with a 400.mu.m diameter photosensitive area coupled to an amplifier as an integrated circuit, and the like. The photodetector has spectral sensitivity in the range of the light transmitted. The photodetector receives an attenuated reflected radiation and converts the radiation into an electrical signal. The detector can also include a thermocouple, a thermistor, and a microbolometer.
Analyte as used herein describes any particular substance to be measured. Infrared radiation detector refers to any detector or sensor capable of registering infrared radiation. Examples of a suitable infrared radiation detectors, include but are not limited to, a microbolometer, a thermocouple, a thermistor, and the like. The combined detected infrared radiation may be correlated with wavelengths corresponding to analyte concentrations using means such as a Fourier transform.
The BT provides the mid-infrared radiation signature and the near-infrared radiation signatures of the analytes present therein. The infrared radiation signature from the BT is affected by the concentration of analytes in the BT. One of the molecules present in the BT is glucose, and the natural mid-infrared or near-infrared radiation signature of glucose contained within the brain tunnel's natural infrared radiation allows the non-invasive measurement of glucose. Changes in the concentration of certain analytes such as glucose, cholesterol, ethanol, and others, may cause an increase or change in the brain tunnel's natural emission of infrared radiation which can be used to measure the concentration of an analyte.
The BT emits electromagnetic radiation within the infrared radiation spectrum. The spectral characteristics of the infrared radiation emitted by the BT can be correlated with the concentration of analyte. For example, glucose absorbs mid-infrared radiation at wavelengths between about 8.0 microns to about 11.0 microns. If mid-infrared radiation passes through or reflects from the brain tunnel where glucose is present, a distinct radiation signature can be detected from the attenuated radiation or the remaining radiation that is not absorbed by the analyte. The absorption of some amount of the radiation that is applied to the brain tunnel (which contains the substance of interest), may result in a measurable decrease in the amount of radiation energy, which can be utilized to determine the concentration of an analyte.
One embodiment of the present invention provides a method and device for non-invasively measuring the analyte concentration in blood or other tissues, and includes the steps of detecting mid-infrared radiation naturally emitted by the brain tunnel, and determining the concentration of said analyte by correlating the spectral characteristics or radiation signature of the detected infrared radiation with a radiation signature that corresponds to the analyte concentration. The method can also include a filtering step before detection by filtering the naturally emitted infrared radiation from the brain tunnel. In the case of glucose measurement, filtering allows only wavelengths of about 8,000 nanometers to about 11,000 nanometers to pass through the filter. The method further includes a detecting step using an infrared radiation detector, which generates an electrical signal based on the radiation received and feeds the signal into a processor. A mid-infrared radiation detector can measure the naturally emitted mid-infrared radiation from the brain tunnel. A variety of detectors can be used including thermocouples, thermistors, microbolometers, liquid nitrogen cooled MTC such as by Nicolet, and the like. A processor can be used to analyze and correlate the spectral characteristics or radiation signature of the detected mid-infrared radiation with a radiation signature of an analyte. For glucose the generated radiation signature is within the wavelength between about 8,000 nm to about 11,000 nm. The method may include an analyzing step using algorithms based on Plank's law to correlate the radiation signature with glucose concentration. The method may further include a reporting step, such as a visual display or audio reporting.
Many illustrative embodiments for chemical sensing were provided, but it is understood that any other sensing system can be used in accordance to the invention. For example a transducer that uses fluorescence to measure oxygen partial pressure, carbon dioxide, pH, nitric oxide, lactate, and anesthetic gases can also be used as well as any other optical chemical sensor including absorbance, reflectance, luminescence, birefringence, and the like.
The eyeglasses of the present invention can include the use of a cantilever system. The present invention preferably includes an arm 2404 held rigidly at one end of the body 2402, represented by a frame of eyeglasses, said arm 2404 having a free end which includes a measuring portion 2406 with walls 2407 which houses sensor 2410. The end of arm 2404 can house any type of sensor or detector such as exemplarily a blood gas analyzer which includes not only a chemical sensor but also a temperature sensor as well as a heating element. It is understood that a variety of sensing systems such as optical sensing, fluorescent sensing, electrical sensing, ultrasound sensing, electrochemical sensing, chemical sensing, enzymatic sensing, piezoelectric, pressure sensing, pulse sensing, and the like can be housed at the end of arm 2404 in accordance to the present invention. Exemplarily, but not by way of limitation, a glucose sensing system comprised of photodetector, filters, and processor can be housed at the end of arm 2404 and operate as sensor 2410. Likewise a combination light emitter and photodetector diametrically opposed or side-by-side and housed at the end of arm 2404 to detect oxygen saturation, glucose or cholesterol by optical means and the like is within the scope of the present invention.
It is understood that plate 2542 can work as a circuit board and house a processor, wireless transmitter and power source. Alternatively, plate 2542 houses a transmitter and power source with signals being transmitted to a remote receiver for further processing and display of results, or plate 2542 holds an antenna for remote electromagnetic powering including passive devices. It is understood that the electronics, transmitter, processor and power source can be housed in a box for implantation under the skin of the animal. In this embodiment the plate 2542 is replaced by this box, and the method includes the step of creating an opening on the skin, and implanting the box under the skin or on top of the skin while arm 2544 preferably remains on top of the skin, and said box is anchored under the skin. A further step may include suturing the skin around the sensor 2550 in order to provide better stability and protection of the sensor, with said suture grasping the skin 2554 on the upper part of brain tunnel 2532 and the skin 2556 in the lower part of brain tunnel 2532, and applying a stitch on edge of each said skin 2554, 2556, said stitch located right above sensor 2550.
The method includes securing plate 2542 to the head of a mammal, preferably by gluing the internal surface of the plate 2542 to the skin of the animal using glue or an adhesive surface; positioning sensor 2550 on the BTT 2532 at the eyelid area 2538, said step preferably accomplished by sliding arm 2544 in a groove 2552 in plate 2542 until the sensor 2550 is on or adjacent to the BTT area 2532. A further step may include bending the free end of arm 2544 and applying pressure at the BTT 2532 by sensor 2550 and producing a signal by said sensor 2550. Further steps include applying an electrical current, and generating a signal by sensor 2550. Other steps may include processing and analyzing said signal, and reporting a value of said signal. Similar steps can be used when applying sensing device 2000, but preferably during human medical use positioning may not include a sliding step.
Now in reference to
Prior art relied on numerical values for guiding a user about exercise intensity, such as looking at a wrist watch to see the value for heart rate from a chest strap monitoring heart beat. Looking at a number has several disadvantages including increasing stress and distraction, both of which can lead to reduced performance. In addition, the human brain is organized in a way to associate indicia such as numbers with a particular information or condition, and that may briefly reduce concentration in the exercise in order for the brain to finish the association, which in this case is for example number 100 beats per minute (bpm) means out of an optimal pulse zone for fitness or number 39.5 degrees Celsius meaning out of optimal thermal zone. Just holding the arm to look at a number may take away precious seconds of performance, since to see a number is necessary to use the ciliary muscle of the eye to focus and also to hold the display in a essentially motionless position such as holding the arm steady and aligned with the eye. In addition, a person older than 45 years of age may have presbyopia and thus have difficult seeing a numerical value unless using eyeglasses. Contrary to those disadvantages of the prior art, the present invention relies on reporting means which do not require using the ciliary muscle of the eye to focus such as in order to read a number. The present invention also is suitable for use by persons of all ages including people older than 45 years of age and with presbyopia and even cataract. In addition the present invention does not require holding a display in an essentially immobile position. Actually reporting means of the present invention are preferably in constant motion during the time of providing the information to the user. Furthermore there is no distraction as trying to read a number and associate that number with a biological condition. Furthermore there is no increased stress as occur when looking and seeing a numerical value, nor extra brain work to interpret a number. All of those advantages are accomplished by using a light source as the reporting means, as in accordance with this invention, said light source adapted to provide information according to the value of the biological parameter. In addition, a light source, such as in a shoe, is naturally present within the visual field of a human without said subject having to directly look or focus at the light. This allows the information to be naturally delivered and effortlessly received by the user. Furthermore the brain through the occipital cortex is better adapted to recognize a visual stimulus than a numerical stimulus and the brain is also better adapted to memorize visual stimuli such as a yellow LED to inform about potential danger than to memorize a number such as 147 bpm or 38.9 degrees Celsius. Furthermore, the information such as a light source is available immediately and without the need for association as occurs with numbers. In addition, the human brain is trained on a daily basis for recognizing and processing visual stimuli, such as green, yellow and red lights in a traffic light or the LED of an electronic device to indicate the device is turned on. Accordingly, the present invention couples the biological aspects related to visual stimuli with engineering and discloses such monitoring device, which preferable include LEDs mounted on or in a wearable article such as clothing, apparel accessories, or shoes as the reporting means instead of numerical values.
Besides temperature and pulse, any other signal can be used including oxygen level, blood pressure, glucose level, eye pressure, and the like as well as signals from other devices such as a pedometer and the like. In addition, the light-based reporting means of the invention can include activation of a light source, such as LED, to indicate the distance or in the case of speedometer to indicate the speed of the user. For example, a user can program the pedometer to activate a light every 1,000 steps or every mile for instance during a marathon. The program is also adapted to activate a LED when the user is running within a certain speed, said speed being predetermined by the user. In this embodiment for example, the pedometer has 3 LEDs blue, green, and red, which are programmed to be activated according to a predetermined speed or distance. For example, the blue LED is activated if the speed is less than 6 minutes per mile, the green LED is activated if the speed is between 6 and 7 miles per minute, and the red LED is activated if the speed is more than 7 miles per minute. The system may also include a global positioning system or other system to track speed and/or distance, with a light being activated when the desired speed or distance is achieved, or alternatively the light is activated when the programmed speed and/or distance is not achieved.
The alert means alert the user when the signals received from a sensor are within appropriate levels or alert the user when the signal is outside levels of safety. For example, alert means inform the user about said user being in an optimal thermal zone (OTZ), in which the body temperature is within ideal levels for example for stimulating formation of heat-shock proteins. The OTZ is considered an appropriate level for health and performance, such as a temperature range between 37.0 degrees C. and 39.4 degrees C., and most preferably around 38.0 degrees C., and even more preferably around 38.5 degrees, up to 39 degrees C., for stimulating formation of heat shock proteins. The OTZ indicates a range of temperature that is safe and that leads to the best performance without overheating. Different levels of OTZ can lead to burning fat efficiently, as burning generates heat which is reflected in an increase in body temperature. Likewise, an optimal pulse zone (OPZ) indicates the optimal range for improving heart fitness. A second zone OPZ-F indicates the range of pulse that can lead to burning fat. A variety of optimal zones can be used and programmed so as to activate the LEDs in accordance with the optimal zone of interest such as fitness, endurance, heart-lung exercise, improving cardiovascular fitness, burning fat, and the like.
The alert means of the footwear or clothing preferably includes a set of lights which are activated according to the level of a biological parameter, such as temperature zone or pulse of the user. One aspect of this invention includes providing an interactive footwear or apparel which helps the user maintain physical activity within an optimal range by visualizing lights and/or listening to sound from shoes and/or apparel. An array of LEDs are mounted on a portion of footwear or clothing which are easily visualized, such as for example the upper portion of a footwear or the portion of an apparel covering the chest or front part of the lower extremities. It is understood that any head mounted gear can also be used with the array of LEDs mounted on a location easily visualized during physical activity. The information about exercise level is then acquired in an effortless way and a natural way. A particular number is not necessary in the preferred embodiment, since the array of lights can indicate the level of exertion and whether the user is within an optimal zone for the planned activity. For example an array of LEDs mounted in the tongue of a shoe or upper portion of a shoe illuminates in a certain manner or flashes in a sequence to indicate the level of a biological parameter, such as pulse level, oxygen level, blood pressure level, or temperature level, or to identify the presence of a chemical substance such as drugs or any analyte present in the body.
In one embodiment an array of LEDs is mounted on the upper portion or tongue of the shoe, said LEDs being electrically connected to a processor which controls and drives the LED array based on an electrical signal, received from a transmitter coupled to a sensor monitoring a physiological parameter. The processor is operatively coupled to a receiver, said receiver receiving signals from said sensor monitoring a any parameter including physiological parameters or environmental parameters such as ambient temperature, humidity, wind and the like, said signals from said sensor preferably being wirelessly transmitted to the receiver in the footwear. In another embodiment the sensor is located in the shoe including sensors for physiological parameters such blood flow, temperature, pulse and any other physiological parameter and/or for detecting ambient conditions such as a ambient temperature, humidity, ultraviolet rays, wind, and the like. In those embodiments there is no need for signal transmission as with remotely placed sensors since the light source is also located in the shoe, and said light source can be integrated with the sensor. The processor is operative to illuminate the LED for a certain period of time preferably in accordance with the user being in the OTZ and/or OPZ, for example by illuminating a green LED. Alternatively, the processing circuit illuminates a red LED to inform the user that the temperature or pulse is too high, or a blue LED to inform that the temperature or pulse is too low, or any combination thereof involving any color or number of LEDs.
The signal from the transmitter coupled to the sensor is transmitted to the receiver in a shoe or clothing, said signal driving a LED or a speaker in said shoe or clothing. For example, when a human subject monitoring pulse and temperature with a BTT sunglasses sends a wireless signal from said BTT sunglasses to a receiver in a shoe worn by said user, and said signal corresponds to an optimal thermal zone and optimal pulse zone, then said signal causes two green LEDs to illuminate in the shoe to indicate that both temperature and pulse are within ideal levels, and causes the shoe to produce the sound “optimal zone”. It is understood that any sound can be produced or any visual indicia can be used to effortlessly and naturally inform the user about the biological parameter level. Accordingly, if the signal received indicates the user is too hot or the pulse is too high, then an indicia representing a Coca-Cola™ logo or a Pepsi-Cola™ logo is illuminated indicating that the user should take some liquid and be hydrated, so as for example to avoid heat injury. Likewise, the signal indicating high temperature can cause the speaker in the shoe or apparel to produce the sound “water”, “time for your Coke™”, “time for your Pepsi™”, and the like. Besides monitoring pulse with a BTT device, any other device for pulse detection including a conventional chest strap for pulse monitoring can be used, said monitoring devices transmitting a signal to a shoe or apparel to drive lights, speaker, and the like. It is also understood that any signal from any device monitoring physiological parameters can be used. Accordingly, a device monitoring glucose, eye pressure, drug levels, cholesterol, and the like can transmit the signal to a footwear or apparel, which cause for example a LED representing low glucose levels to illuminate, and the speaker to produce the sound “sugar low—drink a juice” or the name of a medication is illuminated in the shoe or apparel to indicate the physiological value. Thus when a diabetic is the user of the biological light-sound system of this invention and if the user is monitoring glucose and the word “insulin” is illuminated in the shoe, clothing, or accessories, then that user knows that sugar levels are too high.
It is understood that the housing, referred to herein as module or biological monitoring electronic-LED module, containing the RF receiver, power source, processor, LED, and speaker can be removably attached to the shoe or apparel or permanently mounted on the shoe or apparel. For example a pocket in the shoe or apparel such as a pocket in the tongue of the shoe can be used to house the biological monitoring electronic-LED module. Any pocket or other means to secure one or a plurality of modules to a shoe or apparel are contemplated and can be used. For example, two modules, one for monitoring temperature from a BTT sunglasses is secured by a hook and loop fastener (such as a Velcro™) to a shirt while a second module for monitoring pulse from a chest strap is placed in a pocket located in the tongue of a shoe. When the BTT sunglasses sends a temperature signal to inform the user of the temperature level the LED secured to the shirt illuminates. The same occurs with the LED in the shoe which is activated by a pulse signal from the chest strap.
Now referring to
The module 2610 can include a switch 2622, which can be activated by application of pressure when the shoe is in use or the module 2610 can include a manually operated switch. Module 2610 can include any type of inertia-based switch to allow automated activation of a receiving system of module 2610. Accordingly, when the shoe is not in use or no pressure-based switch is activating the receiving system of the shoe it automatically shuts off. In addition, if the receiving system of the shoe does not receive any signal for a certain period of time, such as for example 10 minutes, then the receiving system of the shoe also automatically shuts off. Those arrangements for automatically turning the shoe on and/or off allows saving battery power and/or making the system of this invention easier to use. If the user wants to know an actual number for the biological parameter, a switch located in the monitoring device coupled to the sensor can be activated or a second switch on the shoe or apparel can be activated and a number can be displayed in the shoe or apparel, or in the monitoring device. In this embodiment, the shoe or apparel, or monitoring device can include a numerical display. For example, it is contemplated that the BTT sunglasses can be adapted to display a numerical value on the lens if requested by the user.
In
Several exercise programs can be implemented with the invention. In order to achieve the proper exercise intensity, the user can use keypads or buttons to enter information into the monitoring device such as the eyeglasses or the chest strap device, or alternatively the user can enter the information in the shoe, said shoe being adapted to receive information and said information including age, body weight, height, exercise goals, and the like. A processor can then calculate the optimal temperature zone and optimal pulse zone for that particular exercise goal which will activate the LEDs in accordance with the signal received and exercise goal. For example, a user 40 years of age, 1.80 m tall, and weighing 95 kg, who wants to have a long workout (more than 45 min) with the objective of burning fat (weight loss), enters the information, which is fed into a processor. The processor is operatively coupled to a memory which stores the OTZ and OPZ associated with an exercise goal and user data. For example according to the user data, OTZ is between 38.1 degrees Celsius and 38.5 degrees Celsius and the OPZ is between 117 and 135 beats per minute (bpm), meaning optimal pulse is between 117 and 135 bpm. A preferred way to calculate the OPZ includes subtracting 220 from the age, which provides 180, and then calculating a percentage of the OPZ number (180) based on the user and exercise goals, which in this example is between 65% and 75%.
The processor is operatively coupled to the LEDs, and in the exemplary embodiment if the temperature signal from the thermometer eyeglasses 2626 corresponds to a temperature higher then 38.5 degrees then LED 2636 is illuminated to indicate the high temperature, translating for example into the need for hydration or reducing exercise intensity since the user is outside his/her OTZ. Likewise, if a pulse signal from heart monitoring device 2624 corresponds to a heart rate less than 117 beats per minute, which is the target for the slowest heart rate, then the processor activates LED 2632 which is illuminated and indicating therefore a slow heart rate for the exercise goal. If the signal received from heart monitoring device 2624 corresponds to a heart rate faster than 135 bpm, which is the target for the fastest heart rate, then LED 2636 is activated and illuminated.
Considering another embodiment with four LEDs comprised of two LEDs marked T and two LEDs marked P, if the temperature falls below 38.1 degrees Celsius a “yellow LED market T” is illuminated indicating low temperature for OTZ, and if above 38.5 degrees Celsius then a “red LED marked T” is illuminated. If pulse is slower than 117 bpm then “yellow LED marked P” is illuminated and if pulse is faster than 135 a “red LED marked P” is illuminated.
An exemplary algorithm for heart monitoring in accordance with this invention is seen in
The invention includes a method for detecting and transmitting a biological parameter, receiving the transmitted signal with a receiver connected to a shoe or apparel, processing the received signal, determining the value of the biological parameter, and activating a light source based on the value. Further step may include activating a speaker. Other steps may include displaying a numerical value and transmitting the signal to another device.
It is understood that the program can be done in sequence, and include other parameters such as oxygen level and uptake, glucose level, blood pressure, acid lactic level, heat shock protein, and any other biological parameter or environmental parameter such as ambient temperature, humidity, wind speed, and the like. All of those parameters are reported using the reporting means of the invention such as the LED system of the invention. Accordingly, in yet another embodiment of this invention, a plurality of array of LEDs are provided. For example a first array of LEDs detects one parameter (e.g. pulse), said array of LEDs separate from a second array of LED measuring a second parameter (e.g. temperature), and both the first and second array of LEDs being separate from a third array of LEDs which measure a third parameter (e.g. environmental humidity). Each group of LEDs can be activated by a signal from a separate transmitter connected to each specific array of LEDs.
It is also understood that each LED can be marked with indicia indicating the physiological condition. Accordingly, an LED can have for example wording “High Temp”, and/or “Fast HR” and/or “Slow HR” in order to report the physiological condition. Furthermore, a speaker or speech synthesizer can be included and concomitantly activated to produce, for example, the sound “High Temp”, and/or “Fast HR” and/or “Slow HR”. It is also understood that LED of different colors to indicate different levels for biological parameters can be used. For example, a green LED represents heart rate less than 130 bpm, a yellow LED represents heart rate more than 130 but less than 170 bpm, and red LED represents heart rate more than 170 bpm. A series of bars can also be used, one bar illuminated indicating heart rate less than 130 bpm, two bars illuminated indicating heart rate less than 170 bpm, and three bars illuminated indicating heart rate more than 170 bpm. The invention further includes a kit containing a device to monitor biological parameter and a shoe or an apparel. The kit can further include instructions. The illuminating device, such as LED, can be also removable to permit interchangeable selectivity of the color of the illuminating light.
Referring now to
It is understood that other receiving devices are contemplated and can benefit from the present invention. For example, an exercise machine can receive the signal and an array of LEDs mounted in said machine indicate to the user the exercise condition and biological parameter values without the user having to rely on a numerical value. Other devices contemplated include a wrist band mounted with at least one LED which is activated based on the level of the biological parameter, said wrist band detecting the level and reporting the level through a least one LED. In this embodiment there is no need for wireless transmission since the wrist band can detect pulse and thus detecting and reporting function are accomplished in the same device. Likewise, a chest strap can have one or more light sources to indicate the pulse level, said chest strap preferably being part of a garment or being under a thin shirt to facilitate visualizing the flashing LEDs. In another embodiment the chest strap monitoring heart rate can include speaker for audio reporting of a numerical value or reporting an optimal zone for exercising such as OPZ or OTZ. It is also understood that a wrist watch can include a set of lights which are illuminated to indicate OPZ and OTZ, or any other optimal value of a biological parameter. Besides, a range and threshold, a mean value can also be calculated and an LED activated to indicate achieving that mean value, or being outside the mean value, such as for example a mean pulse value. It is understood that in addition to illuminating light for feedback, if the user chooses, real-time, spoken feedback can alert said user to milestones, such as number of miles, throughout a workout. It is also contemplated that the shoe or apparel may include a chip that recognizes module 2610, which can work as a removably attached module, so a user can remove module 2610 from one shoe and insert the same module 2610 in or on an apparel or in or on another shoe, so any shoe or apparel with the chip can use the module 2610.
There are basically two types of thermometer probes using contact sensors in the prior art: 1) one for measuring internal temperature such as food thermometers and body temperature such as oral thermometers, which are inserted inside the object being measured, and 2) a second one for measuring surface temperature, such as for instance measuring temperature of a grill. Contrary to the prior art this invention teaches a new method and apparatus which combines in the same thermometer probe features of both internal temperature measurement and surface temperature measurement, such arrangement being necessary for measuring temperature in the brain tunnel.
Thermometer probes for internal temperature measurement of the prior art, such as oral/rectal thermometers, have temperature sensors covered by a metal cap or by other materials which are good heat conductors. The tip of the thermometers of the prior art were made out of metal or other thermally conducting material such as ceramics and the like, including the temperature sensor on the tip being surrounded by a metallic cap. Contrary to the prior art, this invention teaches a thermometer in which the temperature sensor is surrounded by an insulating material. In distinction to the prior art, the thermometer of this invention comprises a tip in which there is no metal or any conducting material surrounding the temperature sensor. The sides of the tip of the thermometer of this invention comprise insulating material, and thus the sides of the tip have at least one insulating layer. In addition this invention couples specialized dimensions with a novel temperature sensing tip that includes an insulating tip instead of a metallic tip, said insulating tip housing the temperature sensor.
Thermometer probes measuring surface temperature are concerned only with the surface being measured and thus do not require insulation in a large area of the probe nor a metallic cover to increase heat transfer. Basically those surface thermometer probes of the prior art have a thermocouple at the end of the probe, said end being rigid and made with hard material.
The design of this invention allows both to be accomplished, measuring internal as well as surface temperature simultaneously. In order to achieve precise surface measurement the BTT sensor is completely surrounded by insulation at the end of the probe. In order to measure internal temperature, the sensor has to enter the tunnel which causes an indentation in the skin. When the probe is pushed into the tunnel because of the characteristics of the BTT area and of skin, there is a rather significant indentation, which leads the skin to encircle and surround the tip, which would lead to affecting the temperature of the thermal sensor since the skin is cold. To prevent that, the probe of the invention has a rather long area (length) of insulating material above the sensor, and no heat conducting material around the tip of the probe, besides the special dimensions previously described. In addition, to conform to the specialized geometry of the skin at the BTT, the insulating material of this invention comprises a soft and preferably compressible insulating material at the tip. Contrary to this invention, the prior art has used hard materials on the tip, since those probes are used for measuring hard and/or flat surfaces, and not irregular surfaces such as the skin at the BTT. In addition, since the BTT geometry is concave in nature, the preferred embodiment of the end of the probe of this invention is essentially convex. Furthermore, the tip of the probe may comprise one or more sensors, and preferably a plurality of sensors disposed in an essentially convex surface. Programming in the processor selects the highest temperature among all sensors facilitating reading the temperature at the main entry point of the tunnel, which has the highest temperature. Preferably, a tip of the probe or the measuring surface of the probe includes both sensor and insulating material in said surface, and said probe is essentially cylindrical. The sensor of this invention which is located at the tip of the probe is surrounded by insulating material, both on top of said sensor and around the sides of said sensor. The sensor of this invention is preferably exposed at the tip of the probe without any material covering said sensor. Contrary to hard insulating material of the prior art, the sensor of this invention is surrounded by soft insulating material. The probe preferably uses a rod and hand held configuration. Contrary to the prior art which uses hard material to support the tip of the probe, such as used in surface measuring thermometer, the present invention uses exclusively soft material around the thermal sensor in its entirety, and no metallic or hard material are adjacent to the sensor or located within 4 mm from the tip of the sensor, this material being illustratively represented in several embodiments including body 2020. The shape of the tip of the probe of this invention is designed to conform and take the shape of the area of the BTT below and adjacent to the eyebrow and the nose, and more specifically to match the roof of the orbit by the nose and eyelid area. The prior art has a very small amount of insulating material around the tip since it was not designed to measure internal temperature. Contrary to the prior art, this invention, by having the necessity of avoiding temperature of the skin that may encircle the probe during entry of the sensor into the tunnel affecting the measurement, a rather large amount of insulation is used. The preferred length of material at the tip of the probe, said insulating material facing the environment, is equal to or less than 3.5 mm, and preferably equal to or no greater than 5 mm, and most preferably equal to or no greater than 10 mm. The insulating material at the tip is preferably not covered by any other material. The thermometer probe of this invention uniquely has features of both types of thermometer, penetrating and surface measuring thermometers. The tip of the thermometer of this invention preferably uses deformable material and conforms to the surface being measured. The tip of the probe takes the contour of the area that is being measured so it seal off any ambient temperature, and prevent surrounding skin tissue around the tunnel from touching the temperature element. Preferably stand alone insulating material is what supports the tip of the probe, said material being preferably compressible material with some springing characteristics. Features mentioned herein have been described in several embodiments of this invention including measuring portion and
In addition, the present invention discloses novel methods and apparatus for measuring biological parameters, such as temperature. Accordingly and in reference to
The electronic device 2702 comprises a touch-screen 2718 which includes a display box 2720 for displaying the numerical value of the signal acquired by the sensor 2704, a second window 2722 to display stored values of the signal being measured, a wire 2714 for connecting the electronic device 2702 with the stylus 2700, and further preferably including a dialog box 2724 for displaying user information such as patient identification, in addition to a processor 2726, and power source 2728. If electronic device 2702 is arranged as a Personal Digital Assistant (PDA), it preferably includes a conventional key pad 2730 for PDAs.
In contrast to the Prior Art,
The intelligent stylus of the invention can be used in the conventional manner with a metal cap, but contrary to the thermometers of prior art, the wire of the intelligent stylus of this invention exit said stylus in the mid-portion of the stylus. As seen in
FIG. 96-G1 shows another preferred embodiment, wherein a cap 2794 housing reagent 2796 such as glucose oxidase is adapted on top of the sensing end 2798 housing sensor 2800 of the stylus 2802. Cap 2794 has arms 2804 for securing cap 2794 on top of sensing end 2798. When blood containing glucose is deposited on top of cap 2794, reagent 2796 generates a reaction which is sensed by sensor 2800, such as an electrochemical or optical sensor, generating a signal that is translated into glucose level after standard processing. FIG. 96-G2 shows in more detail specialized cap 2794 of FIG. 96-G1, which is preferably essentially cylindrical, and houses reagent 2796. Cap further includes arms 2804 and extension 2806 for handling and placement purpose.
Although, a preferred embodiment includes a wired system, it is understood that the intelligent stylus of the invention also includes a wireless system. In this embodiment, as shown in
The end opposite to sensing end 2836 preferably comprises touching end 2844, with said touching end 2844 of the stylus 2830 being preferably free of any sensors and used to touch a surface 2846 of wireless electronic device 2832. This arrangement keeps surface 2846 of wireless electronic device 2832 from being scratched or damaged if the touching end also would house a sensor. Likewise the arrangement prevents the sensor 2834 from being damaged by touching a surface, such as surface 2846.
In reference to
It is understood that any electronic device such as an electronic device which recognizes alphabetical, numerical, drawing characters and the like is within the scope of the invention. An exemplary electronic device includes a device with an electronic surface that recognizes strokes by a writing instrument in which regular paper can be placed on top of said electronic surface for the purpose of writing and converting said writing into digital information by a variety of optical character recognition systems or similar systems, with said writing instrument housing a sensor in accordance with the present invention.
By way of illustration, but not of limitation, exemplary sensors and systems for the intelligent stylus will now be described. The sensor can comprise at least one of or a combination of temperature sensor, electrochemical sensor (such as a blood gas sensor for measuring oxygen), an enzymatic sensor (such as glucose oxidase sensor for measuring glucose), a fluorescent sensor, and an infrared sensing system including a light emitter and a photodetector adapted side-by-side, and using preferably reflectance for measuring the level of a substance, such as glucose or oxygen saturation.
A plurality of sensing and detecting systems are contemplated including an intelligent stylus comprising a microphone and a pressure sensor for measurement of pulse and blood pressure. The end of the stylus preferably houses a piezoelectric sensor to detect sound, and a mechanism to apply pressure, such a blood pressure cuff, in order to change the blood flow and elicit a change in sound. The blood pressure cuff has a wireless pressure transmitter that transmits the pressure information to the electronic device, such as a PDA. When the piezoelectric or microphone of the stylus detects a change in sound it sends a signal to the PDA, which then stores the pressure transmitted by the pressure cuff, creating thus a coupling between the pressure being measured by the cuff and the change in sound detected by the stylus. It is understood that the stylus can include a pressure sensor coupled to a mechanical pressure means that apply pressure in the blood vessel for detection of the mean arterial pressure, and the change in pressure corresponding to the arterial pressure. It is also understood that the end of the stylus of the invention can house a fiberoptic system or other optical system such as system for measuring fluorescent light, and for illuminating the area being measured and identifying the arterial pulse.
Another preferred embodiment includes an antenna with sensing capabilities, the sensing-antenna article comprises preferably a rod-like antenna including a whip antenna and wire antenna which houses in its free end a sensor and the opposite end is void of any sensor and connected to conventional radio electronics or communications electronics and ground plane such as antennas found in cellular phones and radios. Although the sensor is preferably located at the end of the antenna, it is understood that the sensor can be housed adjacent to the free end of the antenna. A preferred embodiment includes a cellular phone housing a temperature sensor at the free end of the antenna, with said cell phone comprising electronic means to convert the sensor signal into a temperature signal, and further means to display by visual, audio, or other indicator the temperature measured. The radio or cell phone of the present invention is adapted to generate and process the signal of a biological parameter being measured with the antenna, thus the cell phone, radio, or other device with an antenna can then function as a thermometer for measuring body temperature using a sensor housed in the antenna. Besides measuring body temperature, the antenna can be adapted to measure temperature in general such as liquids and also for measuring ambient temperature.
Accordingly,
The system can further include a system for measuring wind effect. In this embodiment the temperature sensor is a thermistor. Upon actuation electronics in the cell phone apply current to the thermistor in order to increase the temperature of said thermistor. Since the antenna is exposed to air, the rate of increase of temperature of the thermistor is inversely proportional to the wind speed. With higher wind speed, there is proportionally a need to increase in energy in order to maintain the temperature of the sensor constant. Software can be adapted to identify wind speed, and thus heat or cold index, based on the ambient temperature and the change in temperature of the thermistor being heated up.
It is understood that the sensor at the end of the sensing-antenna or at the end of the sensing-writing instruments can also include a probe cover to avoid cross-contamination when touching a body part, or when touching a drink to measure the temperature of such a drink. It is yet understood that software can be adapted to allow subtle changes in temperature corresponding to ovulation or pre-ovulation to be detected, with said cell phone or radio having means to identify such changes and indicators to display the information about ovulation.
It is understood that a variety of sensing and detecting arrangements are contemplated as shown from FIG. 96-Q1 to FIG. 96-Q4. FIG. 96-Q1 is a planar view of a rod-like sensing device such as a thermometer, a stylus, a writing instrument, an antenna, and the like showing the sensing surface 2912 of a rod-like sensing device having a sensor 2914. Sensing surface 2912 can comprise entirely of a sensor or detector. The preferred largest dimension of sensing surface 2912 is equal to or less than 21 mm, and preferably equal to or less than 15 mm, and most preferably equal to or less than 10 mm. Considering sensor 2914 as a single sensor, the preferred largest dimension of sensor 2914 is equal to or less than 15 mm, and preferably equal to or less than 10 mm, and most preferably equal to or less than 5 mm. FIG. 96-Q2 is a side view of another preferred embodiment showing rod-like structure 2916 having an infrared radiation detector 2918 and sensing surface 2920.
This embodiment of the present invention includes apparatus and methods for measuring brain temperature and detecting analytes in blood vessels directly from the brain by detecting infrared radiation from a brain tunnel. As previously taught the brain tunnel allows direct communication with the physiology and physics of the brain. Blood vessel of the brain tunnel remains open despite circulatory changes and/or vasoconstriction in other parts of the body and/or head.
The most representative and clinically significant representation of the thermal status of the body is brain temperature, and in particular the temperature of the hypothalamic thermoregulatory center. This invention identified a central thermal storage area in the brain around the hypothalamic thermoregulatory center and disclosed the pathway of least thermal resistance to the surface of the body, called Brain Temperature Tunnel because of its ability to work as a physiologic tunnel in which thermal and biological events in one end of the tunnel can be reproduced in an undisturbed manner at the other end of the tunnel. The BTT is an undisturbed and direct thermal connection between this thermal storage area in the brain and a specialized thermo-conductive peri-orbital skin.
This central thermal storage area is represented by the cavernous sinus (CS). CS is an endothelium-lined system of venous channels at the base of the skull creating a cavity working as a pool of venous blood adjacent to the hypothalamic thermoregulatory center. Venous blood in the CS is slow moving which creates a homogenous distribution of thermal energy. Venous blood is the blood type more representative of brain temperature. From a physical standpoint the slower moving blood will generate a lesser thermal gradient between the two ends of a vessel. Arterial blood, such as used in the prior art including temporal artery thermometer, is a fast moving blood which generates a significant thermal gradient and thus void the ability to reproduce accurately core temperature or brain temperature.
This invention identifies unique thermal characteristics only found in the CS. The CS collects and stores thermal energy from the various parts of the brain carried by slow moving deoxygenated blood that is in thermal equilibrium with the brain tissue, namely blood from the cerebral veins, meningeal veins, the sphenopalatine sinus, the superior petrosal sinus, the inferior petrosal sinus, and pterygoid venous plexus. By collecting blood from various parts of the brain, being located in the vicinity of the hypothalamic thermoregulatory center, and having slow moving blood, which allows thermal equilibrium with surrounding tissue and reduced heat loss, the CS functions as a central thermal storage area. While uniquely thermally communicating with various parts of the brain and being located adjacent to the thermoregulatory center, this invention identifies that the CS thermally communicates in an undisturbed manner to the surface of the body through a path of minimal thermal resistance represented by the superior ophthalmic vein (SOV).
To examine the thermal path from brain to skin and create a function for determining the temperature of brain tissue, this invention examined from a thermal standpoint each biological layer between the brain and the skin at the brain tunnel and gave a thermal resistance value to each structure. The temperature gradient between the brain and the skin at the brain tunnel is the summation of the individual temperature gradients across each structure. The lower the thermal resistance between the brain and the measuring site, the less the temperature difference.
Since according to the second law of thermodynamics heat will automatically flow from points of higher temperature to points of lower temperature, heat flow will be positive when the temperature gradient is negative. The metabolism taking place within the brain generates a considerable amount of heat, which the brain must dissipate in order to maintain a consistent and safe operating temperature within the skull. This generates a positive heat flow. When the temperature of the skin area of the brain tunnel and the temperature of the air around the skin of the brain tunnel is greater than the heat produced by the brain there will be a reduction of the positive heat flow up to a point of equilibrium between the brain and the skin area of the brain tunnel.
Most of the heat dissipation is accomplished by direct conduction through the circulatory system. However, the structure which encloses the brain providing physical protection also causes thermal isolation. As can be seen, these two requirements are in opposition to each other. Multiple layers of protection (1. thick skin, 2. subcutaneous tissue, 3. connective tissue aponeurosis (epicraninum), 4. loose areolar tissue, 5. pericranium, 6. cranial bone, 7 dura matter, and 8 cerebral spinal fluid) also represent multiple layers of thermal insulation. Those insulating layers are represented by thermal resistance TR1, TR2, TR3, TR4, TR5, TR6, TR7 and TR8).
This invention identifies that with the exception of the thermal path through the BTT, heat energy flowing from within the brain to the external environment, including the forehead, must pass through about 8 insulating structures, and there is a temperature drop associated with each layer TR1 to TR8. As the heat flows in the direction of the cooler environment outside the body, we traced its path through multiple resistance layers which gives rise to a considerable temperature drop at the surface of the skin in all areas of the body including the head. The outer layer, especially, with a thick skin, fat tissue, and sweat glands (about 5 mm thick) contribute heavily to the thermal resistance equation. The variability resulting from those layers will lead to inconsistent measurements which occur in any skin area in the whole body outside the BTT, which were observed during testing and showed that skin areas outside the BTT area have 1.8 to 7.5 degrees centigrade difference between core temperature and skin temperature in skin areas outside the BTT.
Analysis of the pathway of least thermal resistance from the brain to the surface of the body was performed and the functional and anatomical architecture of the pathway characterized. A model for brain temperature and the thermal resistance pathway was done. The model includes the relationship for heat transfer by conduction proposed by the French scientist, J. J. Fourier, in 1822. It states that the rate of heat flow in a material is equal to the product of the following three quantities: 1. k, the thermal conductivity of the material. 2. A, the area of the section through which the heat flows by conduction. 3. dT/dx, the temperature gradient at the section, i.e., the rate of change of temperature T with respect to distance in the direction of heat flow x. The fundamentals of heat transfer for conduction show that the greater the thermal conductivity, the less is the temperature drop or loss for a given quantity of heat flow. Conversely, the greater the thermal resistance in the heat flow path, the greater the temperature drop. The flow of heat through a thermal resistance is analogous to the flow of direct current through an electrical resistance because both types of flow obey similar equations. The thermal circuit: q=.DELTA.T/R Equation 1-1 q=thermal energy flow, .DELTA.T=the temperature difference between two points, R=the thermal resistance separating the two measuring points The electrical circuit: i=.DELTA.E/Re Equation 1-2 i=the flow rate of electricity, i.e., the current .DELTA.E=voltage difference Re=electrical resistance
The thermal resistance of the various insulating layers surrounding the brain was represented with resistors to evaluate the relative degree of resistance between different possible thermal paths from the brain to the skin. Heat flux sensors were constructed to measure true surface temperature. This is a special temperature probe with two sensors. A thin insulator is placed between the two temperature sensors. One sensor (S1) contacts the surface whose temperature is to be measured (BTT), the other sensor (S2) is on the opposite side of the insulator (facing away from the measurement site). If there is no net heat flow through the insulation layer (Q=0 in equation 1-1), there can be no temperature difference (.DELTA.T in Equation 1-1 must=0) between the two sensors. The control circuit of the heat flux temperature probe provides just enough power to a small heating element next to sensor S2 to equalize or bring to zero the difference in temperature between S1 and S2. By eliminating the heat flow to the external environment we minimize, if not totally cancel, the heat flow from the superior ophthalmic vein to the skin surface under S1. This allows for a very accurate measurement of surface temperature (if Q=0 there is no temperature difference between the vein and skin). By comparing temperature measurements made with the heat flux temperature probe at the BTT site to those made with a miniature temperature probe (very low mass, 38 gauge connecting wires, and well insulated), it was possible to compute the temperature of the heat source (represented by the CS) within the body.
One embodiment includes acquiring radiation emitted from a brain tunnel. Preferably, radiation is acquired using the region between the eye and the eyebrow including scanning and/or positioning a radiation detector over the brain tunnel. Preferably, the brain tunnel area is scanned for about 5 to 10 seconds and the highest peak of infrared radiation from the brain tunnel is acquired, which reflects the peak temperature of the brain tunnel area. Every time a higher temperature is detected a beep or sound is produced, thus when no more beeps are produced the user knows that the peak temperature was acquired. The temperature acquired is representative of brain temperature reflected by blood from the brain. To acquire the core temperature of the brain, a specialized processing is used. The processing may take into account the thermal resistance (TR) of the path between the skin of the brain tunnel and the brain, which can be simplified by using the two main thermal resistances, namely TRB1 (representing thermal resistance due to skin) and TRB2, (representing thermal resistance due to the vascular wall and associated structures). Another factor in the calculation of core temperature may include the thermal gradient between the two ends of the tunnel. Through our experiments including using our fabricated heat flux sensors it was determined that the thermal resistance by TRB1 and TRB2 accounts for up to 0.65 degrees Celsius. Hence in order to determine the core temperature of the brain this invention includes apparatus and methods adapted to perform processing for determining internal body temperature, represented by the core temperature of the brain, illustrated by the equation: T.sub.b=T.sub.bt+TR (Equation 1-3) where T.sub.b is the core temperature of the brain, T.sub.bt is the peak temperature of the skin of the brain tunnel as acquired by the radiation detector, and TR is an empirically determined factor which includes the thermal resistance between the skin of the brain tunnel and the brain.
The processing includes a sum of thermal resistances between the source of thermal energy inside the body plus the temperature of the skin area being measured. Specifically, the core temperature of the brain includes the temperature of the skin at the brain tunnel plus the sum of the thermal resistances of the structures between the skin of the brain tunnel and the brain. More specifically, the preferred processing circuit and processing includes the peak temperature of the skin area of the brain tunnel plus the sum of the thermal resistances between the skin of the brain tunnel and the brain, said thermal resistance comprised of a factor equal to or less than 0.20 degrees Celsius and equal to or more than 0.05 degrees Celsius. Preferably, processing circuit and processing includes the peak temperature of the skin area of the brain tunnel plus the sum of the thermal resistances between the skin of the brain tunnel and the brain, said thermal resistance comprised of a factor equal to or less than 0.30 degrees Celsius and more than 0.20 degrees Celsius. Most preferably, the processing circuit and processing includes the peak temperature of the skin area of the brain tunnel plus the sum of the thermal resistances between the skin of the brain tunnel and the brain, said thermal resistance comprised of a factor equal to or less than 0.65 degrees Celsius and more than 0.30 degrees Celsius. The radiation detector includes a processor and processing circuit having a computer readable medium having code for a computer readable program embodied therein for performing the calculations for determining core temperature, and may further include a memory operatively coupled with said processor, and a display, audio or visual, for reporting a value. Another embodiment includes a further step for determining the brain tissue temperature using the temperature of the skin of brain tunnel that includes a factor pertaining to heat flow and environment temperature around the brain tunnel. To acquire the temperature of the brain tissue (parenchymal temperature), a function taught by the present invention can be used and includes processing in the device to compute the brain tissue temperature based on thermal resistance and the environment temperature around the brain tunnel. The apparatus and methods includes a processing circuit that computes the brain temperature as a function of the temperature of the skin at the end of the brain tunnel and a factor related to the temperature of air within a 90 cm radius from the entrance of the brain tunnel at the skin, described herein as BT-ET300 (brain tunnel Environmental Temperature at 300 cm radius), also referred to herein as BT-300. The BT-300 factor varies with the environment temperature around the area being measured and is based on heat flow. It is understood that this function that includes a factor for each range of environment temperature can be used in other parts of the body beside the brain tunnel.
The BT-300 varies according to the environment temperature around the brain tunnel, or the skin target area being measured. If there is negative heat flow, then the value of the BT-300 is equal to zero in Equation 1-4 below, and equal to 1 (one) in Equation 1-5. If there is positive heat flow from brain to the environment of 0.1 degree Celsius, then BT-300 factor is equal to 1.003. Illustratively, if there is positive heat flow from brain to the environment with a difference of 0.2 degree Celsius, then BT-300 factor is equal to 1.006. If there is positive heat flow from brain to the environment with a difference of 0.3 degree Celsius, then BT-300 factor is equal to 1.009. If there is positive heat flow from brain to the environment with a difference of 0.5 degree Celsius, then BT-300 factor is equal to 1.012. If there is positive heat flow from brain to the environment with a difference of 0.5 degree Celsius, then BT-300 factor is equal to 1.015. If there is positive heat flow from brain to the environment with a difference of 0.6 degree Celsius, then BT-300 factor is equal to 1.018. If there is positive heat flow from brain to the environment with a difference of 0.7 degree Celsius, then BT-300 factor is equal to 1.021. If there is positive heat flow from brain to the environment with a difference of 0.8 degree Celsius, then BT-300 factor is equal to 1.024. If there is positive heat flow from brain to the environment with a difference of 0.9 degree Celsius, then BT-300 factor is equal to 1.027. If there is positive heat flow from brain to the environment with a difference of 1.0 degree Celsius, then the BT-300 factor is equal to 1.030. If there is positive heat flow from brain to the environment with a difference of equal to or more than 1.0 degree Celsius and less than 1.5 degrees Celsius, then the BT-300 factor is equal to 1.045. If there is positive heat flow from brain to the environment with a difference of equal to or more than 1.5 degrees Celsius and less than 2.0 degrees Celsius, then the BT-300 factor is equal to 1.060. If there is positive heat flow from brain to the environment with a difference of equal to or more than 2.0 degree Celsius, then the BT-300 factor is equal to 1.090. Therefore, equation 1-4 provides a method to calculate the corrected brain temperature. T.sub.bc=T.sub.bt*BT-300 (Equation 1-4) where T.sub.bc is the core temperature of the brain corrected for heat flow from the brain, T.sub.bt is the peak temperature of the skin of the brain tunnel as acquired by the radiation detector, and BT-300 is a factor based on the heat flow.
Using equation 1-4, the corrected temperature of brain tissue can be determined with the following equation: T.sub.ct=TR+(T.sub.bt*BT-300) (Equation 1-5) where T.sub.ct is the corrected core temperature of the brain tissue, T.sub.bt is again the peak temperature of the skin of the brain tunnel as acquired by the radiation detector, TR is an empirically determined factor which includes the thermal resistance between the skin of the brain tunnel and the brain, and BT-300 is a factor based on the heat flow.
The method includes the steps of positioning an infrared detector in a diagonal position aiming at the brain tunnel from below the eyebrow, receiving infrared radiation from the brain tunnel, and generating an electrical signal based on the received infrared radiation. The brain tunnel may include an area between the eye and the eyebrow. Further step may include generating radiation or directing radiation by the detector prior to the step of receiving radiation form the brain tunnel. A further step includes processing the signal and determining the body temperature or concentration of a chemical substance or analyte. The body temperature in accordance with this invention ranges preferably from 15 degrees Celsius to 45 degrees Celsius.
Another embodiment of this invention includes a device for removably mounting sensors on spectacles and more particularly to a clip for mounting a sensor on spectacles which includes a spring or a tension ring which provides the force to clamp the spectacles and an adjustably positionable sensor anchored to the clip. The mounting sensing device may further include electronics such as a processor and reporting means such as a LED and/or a wireless transmitter to report the value of a biological parameter. It is understood that a clamp for removably mounting sensors can be adapted for clamping any head mounted gear such as spectacles, headbands, caps, helmets, hats, sleeping masks, and the like.
The invention includes sensors, sensing systems, or detectors including infrared detectors adapted to removably clip onto spectacles in a manner which permits the sensors to be positioned on or adjacent to a brain tunnel. The sensor is more preferably adjustably positionable, and most preferably positioned at the roof of the orbit and between the eye and the eyebrow. The present invention is designed to removably mount sensors or detectors of any type including optical sensors, pressure sensors, pulse sensors, fluorescent elements, and the like onto spectacles or head mounted gear. It is understood that the clip of this invention can be adapted to hold any therapeutic system including drug delivery systems such as for example iontophoresis-based systems, thermal energy delivery devices such as for example thermo-voltaic systems including Peltier systems and gels which change the temperature of the area such as polypropyleneglycol. Any head mounted gear of this invention can hold or house a physical element, electrical device, substances, Peltier devices, resistors, cooling elements, heating elements in a manner so as to position those cooling or heating elements on the brain tunnel area in order to change the temperature of the brain tunnel, and consequently the temperature of the brain. Thus, this embodiment can be useful for therapy of heatstroke and hypothermia.
In accordance with this invention, a clip is provided for mounting sensors on spectacles. Preferably a spring is used to retain the front portion and back portion of the clip together and to provide the necessary force to clamp the frame of spectacles or head mounted gear. Preferably the front portion houses power source and electronics while the back portion houses the sensor. The clip includes electronic housing means, support means, sensor attaching means movably mounted relative to the support means, spectacle clamping means movably mounted relative to the support means and clamping means such as a spring or tension ring.
Support portion 3214 is centrally located and connects the right clamping system 3218 and left clamp system 3222, said support portion 3214 shown housing microprocessor 3236. Left front clamp element 3224 preferably houses power source 3232 and left back clamp element 3226, in the vicinity of the skin preferably houses a light source such as LED 3234. It is understood however, that the LED 3234 can be housed in the left front clamp element 3224, and in this embodiment, LED 3234 may be covering an element such as plastic, said plastic having a logo or other indicia which is illuminated upon activation of LED 3234, which allows viewing of the logo by an external observer. Wire 3242 connects electronic circuit 3236 and power source 3232 to light source 3234 and sensor 3240.
Right and left clamping systems 3218, 3222 are preferably positioned on either side of the nose of the wearer. Front clamping elements 3224 and back clamping element 3226 extend downwardly from a central support portion 3214 and are adapted for clamping a structure such as lenses and frames of spectacles and head mounted gear. Front clamping element 3224 and back clamping element 3226 may operate as legs which are aligned with each other in order to clamp a structure such as spectacles or any head mounted gear. Spring means 3220 is preferably housed in central support portion 3214 and serves to connect the right and left clamping systems 3218, 3222 and to provide the necessary forces for clamping a spectacles frame and for maintaining a stable position for the sensing clip 3212.
The sensor 3240 is preferably disposed along the back portion 3228 adjacent to the skin or on the skin. Sensor 3240 preferably has an arm 3238 for adjustably positioning said sensor 3240. It is also understood that sensor 3240 may include any other structure adapted for adjustably positioning a sensor or detector such as infrared detector on or adjacent to a target area for measuring a parameter. Any of the sensors or detectors described in this invention can operate as sensor 3240. Wire 3242 connects electronics, light source and power source in the front portion 3230 to a sensing system in the back portion 3228.
Arm 3238 may house a wire and may also have a light source disposed in its surface. It is understood that sensing means 3216 does not require an arm to be operative. The sensing means of this invention can include a built-in sensor with no arm, said built-in sensor housed in support portion 3214 or any of the clamping elements of this invention. A variety of clip-on and clamping systems can have a sensor and be used to measure a parameter according to this invention including clip-on affixed with lenses which when in an operative position a lens intersect the visual axis and when in an inoperative position said lens is located away from the visual axis of the wearer.
Upon actuation and pressing the clamps, the upper end of the front portion 3230 and the upper end of the back portion 3228 are brought closed together, causing the front clamping element 3224 and back clamping element 3226 to move away from each other creating an opening for receiving a structure such as spectacles. Upon release of the upper end front portion 3230 and the upper end of the back portion 3228 spring 3220 causes front clamping element 3224 and back clamping element 3226 to be brought together causing clamping of the spectacles or any head mounted gear by virtue of the clamping elements 3224 and 3226.
In another preferred embodiment, as shown in
It is contemplated that any other assembly for clamping, grasping, or attaching a sensing device to eyeglasses or head mounted gear can be used including clamping assembly without a spring. Accordingly, by way of example,
Any attachment means with a sensor for attaching to eyeglasses or head mounted gear is contemplated or any sensing device adapted to be secured to eyeglasses or head mounted gear. Accordingly,
In another preferred embodiment, as shown in
In addition, a sensing device can have arms which wrap around or that are attached to the temples of eyeglasses or to a portion of a head mounted gear. The sensing means may branch off from the sensing device, which is adapted to position a sensor on or adjacent to a target area, such as a brain tunnel. It is also contemplated that any flip sunshades or any type of clip-on sunshades can include sensors for measuring a parameter.
The present invention teaches a modular construction of head mounted gear for measuring biological parameters. Accordingly,
Pulse oximetry module 3526 is located right above the eyebrow 3534 and disposed in the internal face of headband 3520 adjacent to the skin 3536 and includes a pair light emitter-light detector 3582 housed in an adhesive patch 3558 and further includes a wire 3560 which runs on the external surface 3562 of headband 3520 after going through hole 3564 located in headband 3520. Wire 3566 of ear temperature module 3524, wire 3568 of BTT module 3522, and wire 3560 of pulse oximetry module 3526, all run along the external surface 3562 and more specifically sandwiched between a movable lip 3570 which covers the wires 3566, 3568, 3560 and the external surface 3562 of headband 3520. Wires 3566, 3568, 3560 exit headband 3520 and connect to display and processing unit 3572 through connectors 3574, 3576, and 3578.
Pulse oximetry module 3640 is disposed on cavity or recess 3666 on the internal face of headband 3630 and includes a pair light emitter-light detector 3664. Ear temperature module 3638 may include a cord 3646 that terminates in sensing probe 3658 which rests in the ear canal 3668 and receive radiation 3670 from said ear canal. Pulse detection module 3642 and a blood pressure detection module 3644 can include any pressure sensing device, piezoelectric devices, and the like. Brain monitoring module allows directly monitoring of a patient's level of consciousness to help determine and administer the precise amount of drug to meet the needs of each individual patient and to avoid intraoperative awareness. Brain monitoring module works by using a sensor that is placed on the patient's forehead to measure electrical activity in the brain from the EEG and the activity is digitized and displayed as a numerical value. Brain monitoring module allows customized amount of anesthetic and sedative medication to be delivered to the patient and therefore ensure that they are unconscious and free of pain, yet able to wake-up quickly and experience minimal side-effects from anesthesia and sedation. Brain monitoring module 3646 is illustrated herein by three electrodes 3648, 3650, and 3652. The information from the electrodes 3648, 3650, 3652 is processed and a number achieved which provides a direct measure of the patient's level of consciousness allowing clinicians to determine the most effective anesthetic and sedative mix, consequently patients have faster, more predictable wake-ups and higher-quality recoveries with less nausea and vomiting. The brain monitoring module may include an external monitor that analyzes and displays EEG signals, and then converts EEG signals to digital data, and then transfers the data to the external monitor for processing, analysis, and display. Nasal cannula module includes a cannula that goes up over the nose, and preferably not to the sides as per prior art. Modular nasal cannula 3672 is secured by fastening means such as hooks and/or VELCRO and disposed on the surface of the headband 3630. The apparatus and method for supporting the nasal cannula includes a plurality of hooks in the head mounted gear such as a headband of
Pulse oximetry module 3698 is disposed on cavity or recess 3696 on the internal face 3682 of strap 3688 and includes a pair light emitter-light detector 3720. Wire 3722 connects pair 3720 with a display unit (not shown), said wire 3722 being disposed between the external surface 3686 and a lip 3714 after said wire 3722 goes through a hole 3724. Skin temperature sensor module 3700 is disposed on cavity or recess 3694 on the internal face 3682 of strap 3688 and includes a sensor 3726. Wire 3728 connects sensor 3726 with a display and processing unit (not shown), said wire 3728 being disposed along the internal surface 3682 facing the skin 3684. There is also shown the flap 3714, also referred as lip, being connected to external surface 3686 by a hook and loop fastener Wire 3710 connects processor 3712 with a display unit (not shown), said wire 3710 being disposed between the external surface 3686 and a lip 3714, made preferably of fabric or any pliable material.
Pulse oximetry module 3754 is disposed on the cavity or recess 3752 on the external surface 3742, said pulse oximetry module 3754 including a pair light emitter-light detector 3756. Area, recess, or cavity 3752 of strap 3746 has preferably two openings 3758, 3748 for respectively receiving light emitter 3770 and light detector 3772. Light emitter 3770 and light detector 3772 are preferably disposed in a manner to press such emitter 3770 and detector 3772 against skin 3744 and create an indentation. Openings 3758 allow light to be directed at the skin 3744 by emitter 3770 and light to be received by detector 3772 through opening 3748. Plugs 3764 and 3766 are disposed on the bottom of recess 3752 for fastening and firmly securing the module 3754 to strap 3746. Wire 3768 connects pulse oximetry module 3754 with a display and processing unit (not shown), said wire 3768 being disposed between the external surface 3742 and a flap 3758. Internal surface 3778 of strap 3746 may include a peel-back adhesive 3776, which exposes an adhesive surface for more stable securing strap 3746 to a body part. The oxymetry module is preferably located in the headband portion that is above the eye, said oximetry module being next to the module for temperature measurement.
All the modules described herein preferably physically conform to a body portion of a patient, such as a forehead, and provide a firm pressing engagement between the sensors and the living creature's body portion. The pair light emitter-detector may include a flexible structure such as a flexible patch, which is physically conformable and attachable to the subject's body portion. The pair light emitter-detector includes a light source assembly for illuminating the patient's body portion, and a light detector assembly for measuring reflected light. When the pair light emitter-detector is conformably applied to the recess or cavity of the sensing headband, preferably using the snap-on plugs of said headband, localized pressure is exerted on the body portion at the points of contact with the light source and light detector assemblies, and/or the electrodes, and/or the temperature sensors and/or the pressure sensors and pulse sensors, and any of the sensors of this invention.
As in conventional pulse oximetry sensors, the light emitter or light source may include two light-emitting diodes emitting light at red and infrared wavelengths, and the light detector assembly may include a corresponding two or more photodetectors. It is understood that a single light detector can be used to detect light at both wavelengths. The electric signals are carried to and from the light source and light detector assemblies by an electric cable which terminates at an electrical connector, said connector being connected to control and processing circuitry and display.
The present invention teaches a method and apparatus for reusing expensive parts while making the least expensive part, the only disposable part. Electronics and medical sensors are expensive and due to the arrangement of the invention, those expensive parts do not remain in contact with the skin and do not have adhesive surfaces adhering to the skin. The modular construction in which an optical sensor is the only portion touching the skin surface, allows easy cleaning of said optical sensor and reutilization, such as for pulse oximetry. For temperature measurement a very low cost disposable cover is the only disposable material, which is required for covering the sensor that rests on the BTT. Since in the arrangement of the invention, preferably, the electronics, sensors, and other expensive parts do not touch the skin, said parts can be reused. Since the arrangement is done in a manner in which only the forehead material touches the body, and the forehead material is the least expensive of the material sitting on the forehead, and actually really low cost. The device of the invention includes reusable parts and disposable parts.
Brain tunnel module 3982 includes adjustably positionable arm 3400 terminating in measuring portion 3984 illustrated herein by an infrared pair emitter-detector for analyte detection such as glucose and an adjustably positionable arm 3402 terminating in measuring portion 3986 illustrated by an infrared emitter-detector positioned on or adjacent to the brain tunnel next to the bridge of the nose and/or on the eyelid and detecting pulse and oxygen. The housing 3414 of the pulse oximetry module 3990 branches off from the frame 3980 and it is seen located on the right side of frame 3980 with the pair emitter-detector located above the eyebrow 3404. Ear monitoring module 3988 may include a cord 3406, with or without a retractable cable, from the frame 3980, said cord 3406 terminating in sensing probe 3408 which rests in the ear canal and receive radiation from said ear canal. Pulse detection module 3992 branches off the frame 3980 and is adapted to detect pulsation of a blood vessel using a sensor 3416 disposed in said module 3992, said sensor 3416 being located above the eyebrow 3410 and including any pressure sensing device, piezoelectric devices, tonometric device, and the like. Skin temperature module 3996 branches off the frame 3980 includes a temperature sensor 3412 preferably positioned over the temporal artery or in the vicinity of the temporal artery. Behind the ear monitoring module 3994 includes a sensor 3420 located in frame 3980, and more specifically at the end of the temples 3418, and even more specifically at the free end 3422 of the temples 3418. Nasal cannula module 3998 includes a cannula 3999 that goes up over the nose, and preferably not to the sides as per prior art. Modular nasal cannula 3998 is secured by fastening means such as hooks and/or loops disposed along the frame 3980 and illustrated herein by hook-loop 3424, 3426, 3428, on the left side and one hook 3430 illustrated on the right side of frame 3980. By way of illustration nasal cannula is shown on the left side as broken down lines along the frame 3980, but it is understood that said nasal cannula is disposed in the same manner on the right side. Any fastening means to secure a nasal cannula to the frame of eyeglasses can be used.
Wire 3432 connects infrared module 3390 to a processing and display circuit 3434 through electrical connector 3436. Wire 3438 connects ear monitoring module 3988 to the processing and display circuit 3434 through electrical connector 3436. Wire 3440 connects behind the ear monitoring module 3994 to the processing and display circuit 3434 through electrical connector 3436. Brain Tunnel module 3982, pulse detection module 3992, and skin temperature module 3996 connect to a processing and display circuit 3442 through wire 3446 and electrical connector 3444.
Another embodiment includes methods and apparatus for determining and preventing intraoperative awareness and detecting brain activity based on body temperature, more specifically temperature from the BTT.
The method and apparatus includes automated feed back control of an infusion pump based on the BTT temperature for automated and precise adjustment of infusion rate of drugs, such as anesthetics or sedatives, based on body temperature, and more particular core-brain temperature.
A first step determines the body temperature, and a second step determines if the temperature is increased. If yes then increase infusion rate by the pump. With an increased core temperature during anesthesia there will be increased drug metabolism, in which drugs are consumed faster, thus requiring increased infusion rate. With a decreased core temperature during anesthesia there will be reduced drug metabolism, in which drugs are consumed slower, thus requiring decreased infusion rate.
In the Intensive Care Unit, the apparatus and methods adjust rate of infusion of drugs, such as vasoactive drugs, based on the body temperature. With decreased core temperature patient requires warming, which may lead to vasodilation if done in excess leading to hypotension, which then requires administration of costly and dangerous drugs such as vasoconstrictors as epinephrine. Thus, with the present invention by carefully and precisely titrating the warming or cooling of the body based on the core temperature all of those issues can be avoided.
In addition, this invention provides a method and apparatus to determine brain awareness and detect risk of intraoperative awareness. If there is increased temperature during surgery, leading to increased drug metabolism, leading to a more superficial level of anesthesia and risk of intraoperative awareness, thus the method and apparatus of the invention adjusts the rate of infusion and increase the rate of infusion. With increased brain temperature there is an increase in blood flow to the brain, which increases the risk of intraoperative awareness, thus the method and apparatus of the invention adjusts the rate of infusion and increase the rate of infusion. If there is decreased temperature during surgery, leads to decreased drug metabolism, leading to more anesthetic drugs being available, which places the patient at a deeper level of anesthesia, and which can cause complications and death besides increased hospital stay and time for recovery. Thus, with the present invention, the level of anesthetic is precisely titrated and if there is lower core temperature, there is a consequent adjustment of the infusion rate with reduction of the infusion rate. With decreased temperature there is also reduced blood flow to the brain, which decreases the risk of intraoperative awareness, thus the method and apparatus of the invention adjusts the rate of infusion and decreases the rate of infusion. Integration of any pump drug with BTT signal can benefit adjustment of infusion rate of some of the most common surgical procedures including cardiac and cardiothoracic, trauma, neurosurgical, long surgeries, and high risk surgeries and surgeries in which vasodilators cannot be used, or patents with predisposition to shock or hypotension.
There are many clinical benefits due to integration of a BTT signal with a pump, including: 1) Automated and more precise adjustment of flow rate 2) To achieve better depth of anesthesia 3) To reduce risk of intraoperative awareness (increased brain temperature associated with risk of intraoperative awareness) 4) Eliminate/reduce the potential for both under- and overdosing 5) Maintenance of drug levels within a desired range 6) Optimal administration of drugs 7) Reduced drug use 8) Reduced surgical time 9) Reduced assisted ventilation time 10) Reduced ICU time 11) Faster post-operative recovery 12) Reduced hospitalization time 13) Reduced rate of complications intraoperative 14) Reduced rate of complications postoperative 15) Improved and expedited wake-up time from surgery 16) Reduced rate of complications due to hypothermia and hyperthermia 17) Reduced health care cost 18) Improved patient outcome
Integration of infusion pump with BTT continuous signal can benefit adjustment of infusion rate of some of the most common drugs including all injectable anesthetics, propofol, phentanyl, midazolam and other benzodiazepines, insulin, and vasoactive drugs such as nytric oxide and all vasodilators, phenylephrine and all vasoconstrictors. The level of core temperature can also be used to identify effect of drugs and the diagnosis and prognosis of diseases such as Parkinson's, Alzheimer's, and depression. Accordingly
It is understood that any sensor system of the invention can be coupled with finger-like structure, nose bridge, and other structures described in
Another embodiment includes stethoscope connected to a PDA, said stethoscope listening to body sounds such as heart and lung sounds and the PDA recording on digital file the heart or lung sound, and then comparing the sound captured with sounds stored in the PDA memory for determining the diagnosis of the condition.
The invention also includes methods for determining the usable life or function of a sensor based on the thickness of a coating applied to that sensor. Sensor can be covered in parylene and the thickness of the covering used for determining the life of the device. By way of example, a temperature sensor is covered with 100 microns thick layer of parylene which keeps the sensor functioning for X number of days. A 200 microns thick layer of parylene keeps then the sensor functioning for 2X number of days (twice as much) and a 50 microns layer keeps the sensor functioning for ½X (half). As the sensor continues to be used the layer of coating gradually dissolves until total dissolution of the coating exposes the sensor making said sensor inoperative. For example, a temperature sensor ceases to work properly as water and salt from the body reach the sensor and change the resistance after the parylene coating is removed.
Another embodiment includes methods and apparatus for detecting blood flow and diagnosing diseases. The embodiment further includes identifying changes in blood flow of the brain tunnel area after applying drugs locally at the brain tunnel area or systemically by oral or invasive means. The method includes applying, for example, a patch with acetylcholine to identify autonomic dysfunction and the diagnosis of diabetes, heart disease, vascular disorders and the like. Steps include measuring blood flow, applying or delivering a drug, and measuring the blood flow at the same location, such as the brain tunnel area. If there is a sustained change in blood flow at the brain tunnel area, then it is determined that function is normal. If after applying a drug the change in blood flow is not sustained it then indicates autonomic dysfunction.
Another embodiment includes therapy and/or prevention of obesity and reduction of weight through cooling the brain and monitoring the temperature at the BTT. Placing the subject under anesthesia, which reduces core temperature, lowers the temperature of the brain. A preferred step prior to anesthesia is an imaging study such as Magnetic Resonance Imaging to map and quantify the neuronal activity in the hunger center of the brain or other brain areas. Cooling of the body and of the brain is performed in order to cool the hunger center, and therefore reducing neuronal firing in the hunger center, and thus naturally reducing appetite. After the baseline activity is determined, the cooling is performed until core-brain temperature reaches 34 degrees Celsius. When the signal from the temperature sensor, such as the BTT, indicates that level of temperature or other predetermined level, an alarm sounds indicating that target temperature was achieved. Depending on the level of firing of neurons, and the baseline, the anesthesia continues on, with extended periods of anesthesia for people with severe obesity so as to shut down the hunger center and appetite, which can even last 6 months or more. The method and device can include using the area of the BTT between the eye and eyebrow and to cool this area in order to directly reduce brain activity. If a center is hyperactive, then cooling can help stabilize firing of neurons. The method and apparatus can also be used for therapy of a variety of neuro-disorders including stroke, Alzheimer, Parkinson, depression, and the like.
The invention further includes a memory chip housed in the device with a predetermined amount of memory, which correlates to the life of the device. Thus, a chip with capacity for 100 hours of measurements fills the chip memory in 100 hours, and after that occurs the sensing device does not work, and preferably a light on the device, such as body 2002 or an alarm on the screen of the reading unit informs the user that the life of the device has expired.
As seen in
Preferred length of the wing running along the nose 3672, illustrated herein as wing 3644, is equal to or less than 33 mm, and preferably equal to or less than 23 mm, and most preferably equal to or less than 18 mm, and even most preferably equal to or less than 12 mm, said length going from point 3668 to the edge 3678 of the wing 3644. Preferred width of wing 3644 is equal to or less than 30 mm, and preferably equal to or less than 20 mm, and most preferably equal to or less than 15 mm, and even most preferably equal to or less than 10 mm. Preferred thickness of wing 3644 is equal to or less than 25 mm, and preferably equal to or less than 20 mm, and most preferably equal to or less than 15 mm, and even most preferably equal to or less than 10 mm.
The bulging connecting portion 3658 is the portion adapted to best fit with the main entry point of the tunnel and is located adjacent to the junction of the eyebrow 3666 with the bridge of the nose 3672. Preferred dimension or diameter of the bulging connecting portion 3658 is equal to or less than 30 mm, and preferably equal to or less than 25 mm, and most preferably equal to or less than 20 mm, and even most preferably equal to or less than 15 mm. Preferred thickness of portion 3658 is equal to or less than 30 mm, and preferably equal to or less than 20 mm, and most preferably equal to or less than 15 mm, and even most preferably equal to or less than 10 mm.
Processing circuit, such as processor 3624, screens and selects the most optimal signal, depending on the application, from the plurality of signals received from the plurality of sensors. In the case of thermal sensors, processing continuously screens and then selects the highest temperature, which is then reported. One or multiple sensing points can be checked periodically and one or more signals can be selected and displayed. For temperature measurement the thermal sensors are imbedded in an insulated material shaped to fit into the anatomical and thermal characteristics of the BTT pocket for easy placement and optimal heat transfer. Thermal sensor is preferably encapsulated and surrounded with a soft thick, non-conductive, insulating material that will take the contour/shape of the irregular skin surface to completely seal off any external ambient temperature and also to prevent any skin or tissues outside the BTT entrance site from touching the sensor.
Since folds of skin can touch the tip of the sensor head when is pressed against the BTT, the sensor head has a unique and specialized dimension of insulating material surrounding the sensor, which is preferably between 3 mm and 5 mm, and most preferably between 2 mm and 7 mm, and even most preferably between 1.5 mm and 10 mm as seen in
The sensing systems of this invention measures, records and/or processes feedback information for a closed loop system and controlling a second device, such as the infusion pump of
It is understood that other configurations of the modular design of the invention would be apparent to one of ordinary skill in the art. Other configurations using other head mounted gear such as a cap, eyewear, and the like are contemplated. Those head mounted gear positions and secures the sensor assembly as a docking device and can measure, record, feedback multiple parameters in a modular design such as pulse oxymetry, heart rate, temperature, and the like.
It should be noted that this invention provides not only measurement, recording and processing of a biological parameter such as temperature but also includes a device that will house the therapy. By way of illustration, the modular forehead docking system of this invention can include a mechanical holding and positioning structure for a cold or hot element or substance that is placed on the BTT site for cooling or heating the brain including a thermo-voltaic device such as a Peltier device, serpentine for circulating fluids, and the like. The head mounted gear such as the head band of this invention can also be an electronics structure positioning, powering, and controlling device to heat or cool the BTT site. The module of the sensing head band includes controlling/processing circuit that can work as a close loop device itself for therapy, by having one side a BTT thermometer and the other side the cold/hot device on the BTT site, providing thus an independent medical close loop monitoring, controlling and cooling/heating device.
The module of the sensing head band box is also designed to analyze a temperature signal or other biological signal and correlate it to other patient data and display other parameters either on the sensing head band device or transmit the information via wire or wireless means to another host monitor or device. The parameters that the system correlate/calculate/analyze include sleep disorder patterns, Alzheimer syndromes, obesity parameters, calorie burns for weight control, fatigue/drowsiness, ECG/EKG, brain wave patterns, and the like.
The present disclosure provides a medical device for monitoring biological parameters through an Abreu Brain Thermal Tunnel (ABTT), which was previously described as a brain temperature tunnel, and which is described in more detail in U.S. Pat. Nos. 7,187,960, 8,172,459, 8,328,420, 8,721,562, 8,834,020, and 8,849,389, incorporated herein by reference in its entirety. Contrary to previous disclosures, the Applicant of this current disclosure recognized that the structure was not a brain temperature tunnel, but indeed a brain thermal tunnel, in which measurement of temperature is only one feature among many, including brain thermal patterns (which are subject of this disclosure), and that this newly identified and characterized Brain Thermal Tunnel is part of a complex thermodynamic system and includes, by way of illustration, an intra-brain thermodynamic subsystem, a brain-heart thermodynamic subsystem, a brain-hormonal thermodynamic subsystem, and brain-environment subsystem, all of which are objects of the present disclosure.
The ABTT comprises a continuous, direct, and undisturbed connection between a thermal energy source within a human brain and an external point on the facial skin at the end of the tunnel. The physical and physiological events at one end of the tunnel are reproduced at the opposite end. The ABTT allows direct thermal energy transfer through the tunnel without interference by heat absorbing elements. The source of the thermal heat in the brain is the region of the brain that is a control center for involuntary functions of the body. More specifically, the ABTT terminates adjacent the hypothalamus. The recipient of the thermal heat is four veins that converge to an ABTT “target area” or “terminus,” which is at the facial end of the ABTT. The target area measures about 11 mm in diameter, measured from the medial corner of the eye at the medial canthal tendon and the lacrimal or tear puctum and extending superiorly for about 6 mm, and then extending into the upper eyelid in a horn-like projection for another 22 mm. Applicant recognized that blood flow in the ABTT is minimal or stagnant, and, in contrast with other portions of the circulatory system, is bi-directional. Furthermore, Applicant recognized that temperature in the area of the hypothalamus was, contrary to conditions in other portions of the body where temperature is measured, constantly varying. Applicant also recognized that the area of the brain around the hypothalamus has specialized thermodynamics. Still further, Applicant determined that the variation in thermal status presented substantial potential for monitoring the condition of a person because of the speed of temperature variation was indicative of the performance and condition of the body. However, considering that the potential for the ABTT is presently unappreciated, equipment for monitoring the ABTT is presently unavailable. Accordingly, the present disclosure presents configurations for monitoring the facial terminus or end of the ABTT, and for precisely measuring brain temperature and thermal milieu.
The ABTT is located in a crowded anatomic area. Therefore, the positioning of an apparatus to gather data from the ABTT requires special geometry for direct contact with the ABTT target area and for optimal thermal transfer, and for non-contact capturing of thermal energy from the area. Four facial veins converge at the ABTT target area: frontal, superior palpebral, supraorbital, and angular/facial. The angular/facial vein extends from the ABTT target area, running alongside the nose, and then extending toward the cheek; the superior palpebral vein extends from the ABTT target area to run along the eyebrow; and the frontal and supraorbital veins extend from the ABTT target area to run upwardly across the forehead. The ABTT target area is the only location where four veins converge, connecting the center of the brain to the skin. Additionally, the ABTT target area has special vasculature and is the only skin area in which a direct branch of the cerebral vasculature is superficially located and covered by a thin skin without or in the absence of a fat layer. The main trunk of the terminal branch of the superior ophthalmic vein is located right at the ABTT target area and just above the medial canthal tendon supplied by the medial palpebral artery and supra-orbital vein. The ABTT target area on the skin, supplied by a terminal and superficial blood vessel ending in a particular area without fat and void of thermoregulatory arteriovenous shunts, provides a superficial source of undisturbed biological signals including brain temperature, heart rate, blood pressure, blood flow, oxygen levels and oxygen saturation, and body chemistry such as glucose level, and the like, besides carbon dioxide and other gases.
The present disclosure provides answers to apparent meso-skeletal, venous, and arterial flaws, and aberrations that endanger life, and includes multiple apparatus and methods for measuring, decoding, and analyzing signals from not only the ABTT, but also all associated neural, vascular, and hormonal links including the aberrations. Why is the brain protected with a thick skull, but leaves a hole that is covered by the thinnest, fat-free skin? Why does the tunnel contain a valveless vein that courses along a transverse axis and facilitates spread of infection (including acne) from the “death triangle” of the face to the cavernous sinus (CS), potentially killing the otherwise young and healthy by CS thrombosis and infection? Why encircle this vein with fat, have it course without an artery and carry deoxygenated blood to an oxygen-demanding organ? Why have the cerebral venous (CV) system carry waste products/metabolite-laden blood to a stagnant pool adjacent to the brain (CS)? A potential intracranial fatal relationship also occurs with the arterial system; the ICA makes a sigmoidal turn through the CS. Why predispose to carotid-cavernous fistula and potentially fatal cerebral hemorrhage by combining two dissimilar pressure structures (artery-vein) and why cause turbulence, with an S-shaped vessel, that may damage blood cells and vessel wall?
When viewed from a matter (structure, blood flow) standpoint, the aforementioned configurations appear to be morphological and physiological aberrancies at best and lethal flaws at worst. However, the information provided in the present disclosure showed that the aberrancies and ABTT should be viewed from thermal and electromagnetic perspectives. The answer to the question revealed herein is thermodynamics. As shown by dissection, fat arrangement in the ABTT enables non-dissipated transmission of thermal energy between brain and surface; this insulated configuration is even more significant as low velocity blood in the superior ophthalmic vein (SOV) facilitates thermal exchange with surrounding tissues, thereby eliminating the thermal integrity of the passage. Thermodynamics also explains the large-sized vein and slow moving venous blood (since these provide optimal thermal carrying capabilities) and the lack of a parallel artery (since this configuration avoids counter-current heat exchange in the ABTT). SOV and the cerebral venous system as shown herein play a role in the context of thermal information, regulation, and/or exchange systems.
Thermodynamics also elucidates arterial “aberrancies.” Thermal exchange between CS and arterial blood coursing rapidly through a straight vessel would be minimal. However, Applicant recognized that the S-geometry of ICA as it courses through CS increases surface area in contact with CS, decreases blood velocity, and changes flow from laminar to turbulent (high Reynolds number); the combination promotes efficient thermal transfer across the ICA wall. When those thermodynamic factors are accounted for, Applicant further recognized that the potentially enhanced thermal transfer ICA-CS justifies the S-geometry and combining dissimilar pressure structures and arterial-venous blood into one structure.
In
In the present disclosure, Applicant also reveals a previously unappreciated perihypothalamic triunal thermo-sensory/regulatory system, which is the object of various embodiments in this disclosure, as shown in
In addition to thermal communication, apparatus and methods of the present disclosure identified and decoded light transmission via this energy path, including phototransduction, by the proximity of the ABTT terminus to the suprachiasmatic nucleus in the brain as well as the unexpected presence of photoreceptors in the hypothalamus. The apparatus and methods disclosed herein identified, decoded and analyzed: (i) unknown brain/core thermal discordance; (ii) unknown brain signals from heat exposure, exercise, surgery; (iii) unknown cerebral neuronal activity, (iv) unknown brain signals from sleep, awakening, arousal, seizures; (v) unknown heat generated by human thought; (vi) unknown spectral and fractal patterns that characterize cerebral thermodynamics; and (vii) unknown brain oscillatory signals. The present disclosure transforms temperature from a non-cerebral dichotomous (febrile/afebrile) variable into a brain oscillating signal for monitoring anesthesia/surgery, behavior/cognition, exercise, fever/pyrogens, heatstroke, hypothermia, ovulation, and populations threatened by bioterrorism, pandemics, and heat waves while providing a tool for reducing livestock carbon footprint. The embodiments provide thermo-diagnostic information and/or information on mis-folded proteins including Alzheimer's, Parkinson's, multiple sclerosis, and diabetes. The cerebral bidirectional energy path disclosed herein allowed embodiments that can impact the brain from an external signal, input, or stimulus for diagnosing and treating various conditions and disorders.
The present disclosure examined the limited arrays of fat within the cranium from a new thermal energy perspective, distinct from the established role of fat in limiting heat transmission between core and surface. Usually fat is discarded during dissections. However, in light of its low thermoconductivity (k) [k=0.00004 Kcal/(s·N·C)] (6), this fat was the prime target of the macroscopic and microscopic search of this disclosure for low-k tissue configured as a thermally transmissive path.
Especially since there is no fat in the cranial cavity and the brain does not use fatty acids as energy source, Applicant was intrigued by large orbital fat pads (OFP, the predominant nonocular tissue within the orbit; e.g., see
To further support that this fat-enclosed path revealed herein constitutes a tunnel for undisturbed brain⇄surface thermal transmission was support by three additional experimental evidence and analysis disclosed by the present disclosure: 1) the contents of the tunnel suitable for undisturbed thermal energy transfer; 2) the internal end of the tunnel is configured for thermal energy transfer to/from brain; and 3) the peripheral end of the tunnel is configured for thermal energy transfer to/from body surface.
The thermodynamic configuration disclosed by the present disclosure is verified by what passes through and what does not pass through the tunnel. The insulated horizontal path-contains an optimal thermal energy carrier, slowly moving blood in a uniquely valveless and large vein, the SOV; coursing between the superomedial orbit (and the eyelid) and the cavernous sinus (CS) (e.g., see
At its intracranial terminus, the ABTT continues until the SOV passes through the superior orbital fissure to terminate at the CS (e.g., see
The aforementioned low-k walled path (ABTT) provide insulated heat convection (conduction) through the orbit, and thereby facilitates thermal exchange with facial blood, which is subject of an apparatus and method of the present disclosure. The ABTT disclosed herein prevents dissipation of thermal gradients during passage of the SOV within the orbit.
However, the path from the brain alone would not enable totally undisturbed brain⇄surface transmission. Without a high-k external terminus, direct (e.g., radiant) transfer of thermal energy at the body surface would be prevented by the cranium's seemingly omnipresent adipose and skeletal wall. This not only would preclude surface measurement of brain temperature but also impede effective brain⇄surface thermal communication and heat dissipation. Other sites, including forehead (FH) (see, e.g.,
Multiple embodiments that decoded brain information are disclosed in the present disclosure. Embodiments also extract and deciphered thermal and electromagnetic transmission between brain and this newly identified high-k skin surface. Cerebral information previously unknown was recognized, decoded, and analyzed in both humans and animals by the various embodiments disclosed herein. The disclosure includes apparatus and methods for capturing and coding thermal emission via the ABTT. Other embodiments altered cerebral neuronal activity and/or inducing brain/core discordance in humans and animals, with the brain information generated being decoded and analyzed.
The present disclosure also discloses a tunnel-enabled thermo-sensory and thermoregulatory triunal configuration, which is an object of various embodiments shown herein. This disclosure further recognized and decoded light emission from the ABTT and showed that works as black body radiant. The thermodynamic configuration described herein unearthed the development of apparatus and methods to measure or alter thermal transmission by acting on a link between neural (and brain), and vascular systems.
Table 1 provides the thickness (in microns) of the layers of skin and fat. The two BTT skin specimens were the only areas with the same dermis thickness and no SC fat.
Applicant's studies of brain and cerebral thermodynamics showed a hidden and encrypted phenomenal system in the brain, referred herein as the Abreu Brain Thermal Tunnel (ABTT), and also as the less precise Abreu Brain Temperature Tunnel. Applicant reveals that fat distribution in the cranium and associated brain structures creates a thermodynamic configuration for brain thermal transfer in humans and animals, which is the subject of various inventions in the present disclosure, including the apparatus and methods described herein.
The present disclosure capitalizes on new information from a new understanding of the ABTT and how it functions, from which Applicant recognized certain characteristics amenable to measurement and analysis that lead to improved diagnostics of human subjects and animals. Moreover, in the present disclosure, Applicant reveals a hitherto unappreciated distinction in the brain path of humans and animals, which is reflected in the apparatus and methods for humans and animals disclosed herein.
The inventions of the present disclosure also extract from the cerebral thermodynamic configuration revealed herein a useful signal that, by being decoded by the apparatus and methods of the present disclosure, provide information that, prior to the inventions of the present disclosure, was previously only available to the brain. With the apparatus and methods disclosed herein the information is decoded and analyzed so as to be available for the benefit of humanity through the diagnosis of diseases, analysis of non-disease human biology, the treatment of diseases, and the cure of maladies.
The present inventions decode signals from the brain that contains information previously unknown and unavailable in the current body of knowledge of the world. With the inventions of the present disclosure, it is possible to decode information that reveals a brain thermal or thermodynamic communication and exchange system, which provides early diagnosis of myriad pathologic and physiologic conditions, the ability to treat diseases, and potentially even to extend longevity, which may enable humans to reach the age of 120 years in full vitality. Applicant's research shows that thermodynamics is the basis for, and the main form of communication in, the brain, but this communication information was unknown prior to this disclosure, and the information is encrypted. The apparatus and methods of the present disclosure reveals information that was previously privy to the brain only, and that information is related to keeping the body functioning and enabling humans and animals to remain alive and well. Applicant's research further showed that the body as a whole, and more specifically the structure of the cranium and brain, is designed with the purpose of this thermodynamic configuration generating signals for brain function and preservation of life, to the extreme that the brain and body jeopardize life itself for the sake of brain thermodynamic communication.
The ABTT also explains aberrancies in the body and brain, even lethal aberrancies, and the present disclosure shows how to use those aberrancies to preserve life, with the apparatus and methods showing how to extract and decode the signals ranging from heart-brain thermodynamic structures to intra-brain thermodynamic information and configuration. The coded information that was previously a privilege of the brain is only now being decoded with the present inventions for the benefit of humanity and reduction of human suffering.
The inventions of the present disclosure work to assist the brain in performing its function in an optimized manner, and by knowing the way the brain communicates and functions the inventions of the present disclosure assist the brain in times in which brain reserves are exhausted, or when the aging brain no longer can function adequately, the inventions of the present disclosure provide the means and support needed to enhance and restore brain function, ranging from the use of electromagnetic means (all wavelengths in the spectrum) and ultrasound to pharmacological means. The inventions of the present disclosure also provide apparatus and methods that allow the brain to fight diseases. Other associated means (including pharmacological and drugs) assist the brain, but the central point is the brain, such brain function being enabled and facilitated by the devices, systems, methods, and drug delivery systems disclosed herein. By way of illustration, but not of limitation, in some embodiments the current disclosure provides the extra “troops” that are missing in the brain (due to disease or other conditions including genetic conditions), said troops being thermodynamic and thermal means that, added to any available natural brain means, enables the brain and associated body to fight a variety of conditions and diseases ranging from infections to cancer, and even altered genetics. Embodiments of the inventions of the present disclosure decode the brain thermal transfer signals present in the ABTT, and provide the extra “troops” needed to restore brain function and to protect the body.
A fat-based thermoconductive configuration revealed herein in the ABTT allowed creation of apparatus and methods that revealed brain thermal transfer mechanisms, said apparatus and methods provide codes and patterns associated with cerebral neuronal activity and delineation of said activity. Viewed herein from macroscopic/microscopic thermodynamic perspectives, the path between cavernous sinus and uniquely thermoconductive orbital and eyelid skin provides the basic structure of the ABTT, allowing the apparatus and methods disclosed herein to overcome the body's natural thermal barrier. ABTT generated the highest radiant surface and the inventions of the current disclosure decoded the light emission that contains vital information only previously available to the brain itself. The apparatus and methods described herein transformed a non-cerebral dichotomy (febrile/afebrile) into continuous oscillatory cerebral signals providing spectral-domain thermal characterization of REM sleep (Rapid Eye Movement phase of sleep) with identification of the frequency band (0.01 Hz; see
The inventions of the present disclosure helped to identify and decode brain (ABTT)/core discordance in anesthesia, surgery, exercise, seizures, arousal, and sleep reaching even 5.6° C. Apparatus and methods of the present disclosure provide means for monitoring psychological, physiological, and pathophysiological processes, in addition to providing means for monitoring public health such as pandemics, agro-terrorism, and heat waves. The inventions of the present disclosure also helped to identify and decode thermal milieu for protein folding and triunal thermoregulatory/sensory morphologies that contains signals essential to survival.
The apparatus and methods provided herein include the means to decode signals in the sick (with fever) to robust (with heatstroke), including: (i) psychological assessment by the apparatus deciphering codes associated with aggressive behavior, depression, emotions, illicit drug use, interpersonal behavior, neurocognitive dysfunction, and sexual behavior; (ii) physiological assessment by the apparatus deciphering codes associated with longevity, fatigue, sleep, pre-ovulation and ovulation, hydration status, electrochemical and electrolytic status, and sexual activity and pleasure; (iii) pathophysiological assessment by the apparatus deciphering codes associated with hormonal disorders, neurological disorders, vascular and cardiac disorders, respiratory disorders, infectious disorders, metabolic disorders, cancer, coma, sudden infant death syndrome, brain trauma, foot-and-mouth disease, and protein folding in a variety of disorders including, but not limited to Alzheimer's Disease, Parkinson's disease, diabetes, Huntington's disease, amyotrophic lateral sclerosis, and multiple sclerosis; and (iv) treatment of disorders by the apparatus deciphering codes associated with therapy of various diseases, and by way of illustration, but not of limitation, treatment ranging from cancer to neurologic diseases and from stroke to coma and sleep disorders. Apparatus and methods of the current disclosure, by deciphering and documenting cerebral thermal milieu, allow understanding psychological, physiologic, and pathophysiologic processes, with creation of inventions for detecting and treating protein mis-folding, abnormal enzymatic reactions, and altered circadian rhythms.
Prior art has not been able to achieve any of the objects of the present disclosure because among the many limitations and drawbacks of the prior art, the sites where measurement is taken is not suitable for or capable of generating adequate signals. For example, skin throughout the body (except in the ABTT) is structured for thermal insulation, not thermal transmission. Other prior art means involve invasion of organs, but such organs used as a source of thermal information are not structured for delivering thermal signals, being structured for hearing (ear thermometer), breathing (nasal thermometers), ingestion (oral and esophageal thermometers), and excretion (rectal and bladder thermometers). All of the aforementioned sites contain components and/or contents that impede measurements. Limitations of the prior art prevent adequately answering a simple question: “Does an individual (human or animal) have fever?” as one site indicates normothermia and another simultaneously indicates fever. Even children in intensive care are not spared, with practitioners pleading: “Can there be a standard for temperature measurement . . . ?”
Applicant examined tissues from a physics perspective, shifting from seeing tissues solely as matter to viewing tissues, macro- and microscopically, as components of thermodynamic systems. Applicant searched for low thermoconductivity tissues, viewing insulation as an indicator of a conductor of thermal energy within the cranium. This formerly hypothetical thermal conductor would require a pathway encircled by fat, the lowest thermoconductivity tissue at 0.00004 Kcal/(s·N·C). Dissections revealed the orbital fat pad to be uniquely configured as an insulated thermal tunnel, surrounding the superior ophthalmic vein (SOV) (e.g., see
The CS (e.g., see
Cerebral venous blood (e.g., see
Table 1 provides measurements of the thickness of fat and dermis in the axillary (armpit), neck, forehead, and the skin adjacent to, over, or on the ABTT terminus. The measurements were from dissections performed on cadavers fixed in 4% formaldehyde. Fragments of skin and underlying tissue from the SMO and eyelid, forehead, neck, and axilla, were embedded in paraffin, sectioned, and stained with HE (hematoxylin and eosin stain) and Masson's trichrome. Dissection was performed to expose the anatomy underneath the SMO and its continuity to the brain. Photomicrographs were obtained and histomorphometry performed.
The results show that the axillary, neck, and forehead had palisades of fat and thick dermis, both of variable thickness (measured in micrometers in Table 1). In contrast, SMO and eyelid skin over the ABTT of all cadavers showed no fat and a commonly thin dermis. Gross anatomic dissection confirmed that this thin, fat-free skin was directly over the aforementioned brain thermal tunnel, which is consistent with thermograph documentation that infrared radiation from this region exceeds that of all other sites on the face and forehead, and the remainder of a human body.
All sites other than the SMO and superior medial eyelid used for surface thermometry must overcome a thick insulatory wall, including fat with the thermal conductivity comparable to oak at 0.00004 Kcal/(s·N·C). The thicknesses shown herein accounts in large part for differences and variability in temperature found among non-SMO surface sites, e.g., the axillary, forehead, and neck, including corresponding forehead sites on different cadavers. Application of an offset to adjust for the insulating nature of fat and dermis is complicated by variations in insulatory layers among individuals, among sites on the same individual, and over time at the same site on the same individual. The differences and inconsistencies due to this variable thermal wall are critical not only for quality patient care, but also for documentation and adherence to monitoring guidelines and requirements (e.g., Surgical Care Improvement Program or SCIP) in different perioperative locations (e.g., operating room, Intensive Care Unit or ICU).
The medical devices disclosed herein may include a modular configuration, including an electrically isolated microprocessor based system, which may be described as an Interface Module System (ISM), which interfaces with a sensor and a computing device, such as an external computer, tablet, cell phone, watch, eyeglasses, or the like, with the ISM providing signals to a second module that includes a personal computer (e.g., a computer with a Windows operating system; a computer with a Macintosh operating system; a computer with a Linux operating system, a computer with Android operating system, any electronic device with computing capabilities, and the like). The personal computer hosts software configured to analyze the signals provided by the sensor to determine a condition of a biological activity, such as brain function, illness, organ function, etc.
An exemplary embodiment ABTT monitoring system 8000 is shown in
ABTT monitoring system 8000 may be configured to be an electrically isolated microprocessor-based interface providing temperature readings from the attached thermistor temperature sensor to an internal or external controller. Many aspects of the disclosure are described in terms of sequences of actions to be performed by elements of a computer system or other hardware capable of executing programmed instructions, for example, a general-purpose computer, special purpose computer, workstation, or other programmable data process apparatus. It will be recognized that in each of the embodiments, the various actions could be performed by specialized circuits (e.g., discrete logic gates interconnected to perform a specialized function), by program instructions (software), such as program modules, being executed by one or more processors (e.g., one or more microprocessors, a central processing unit (CPU), and/or application specific integrated circuit), or by a combination of both. For example, embodiments can be implemented in hardware, software, firmware, microcode, or any combination thereof. The instructions can be program code or code segments that perform necessary tasks and can be stored in a non-transitory machine-readable medium such as a storage medium or other storage(s). A code segment may represent a procedure, a function, a subprogram, a program, a routine, a subroutine, a module, a software package, a class, or any combination of instructions, data structures, or program statements. A code segment may be coupled to another code segment or a hardware circuit by passing and/or receiving information, data, arguments, parameters, or memory contents.
The non-transitory machine-readable medium can additionally be considered to be embodied within any tangible form of computer readable carrier, such as solid-state memory, magnetic disk, and optical disk containing an appropriate set of computer instructions, such as program modules, and data structures that would cause a processor to carry out the techniques described herein. A computer-readable medium may include the following: an electrical connection having one or more wires, magnetic disk storage, magnetic cassettes, magnetic tape or other magnetic storage devices, a portable computer diskette, a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (e.g., EPROM, EEPROM, or Flash memory), or any other tangible medium capable of storing information. It should be noted that the system of the present disclosure is illustrated and discussed herein as having various modules and units that perform particular functions.
It should be understood that these modules and units are merely described based on their function for clarity purposes, and do not necessarily represent specific hardware or software. In this regard, these modules, units and other components may be hardware and/or software implemented to substantially perform their particular functions explained herein. The various functions of the different components can be combined or segregated as hardware and/or software modules in any manner, and can be useful separately or in combination. Input/output or I/O devices or user interfaces including, but not limited to, keyboards, displays, pointing devices, and the like can be coupled to the system either directly or through intervening I/O controllers. Thus, the various aspects of the disclosure may be embodied in many different forms, and all such forms are contemplated to be within the scope of the disclosure.
By way of illustration, but not of limitation, ABTT monitoring system 8000 is a single channel electronic instrument intended principally for sensing and monitoring patient temperature. However, it should be understood that a multi-channel system with multiple sensors and detectors for monitoring various biological parameters is within the scope of the disclosure. ABTT monitoring system 8000 includes a temperature sensor, such as the temperature sensors shown in
Returning to
Analog dial gauge or display 8010 includes a pointer 8020 to indicate the temperature received from an associated temperature sensor by pointing to a value near a periphery of the gauge or display. The display may include a single unit of measure, such as Celsius, or may present more than one unit of measure. System display 8001 may include a “units” switch 8036 to select which unit(s) is or are displayed on dial gauge or display 8010. As shown in
To move the positions of high limit pointer 8016 and low limit point 8018, system display 8001 may include dedicated high and low limit set point switches, such as high limit set switch 8022 and low limit set switch 8024. Positioning of high limit pointer 8016 and low limit pointer 8018 may be accomplished by move the associated high limit set switch 8022 or the low limit set switch 8024 into the “−” or “+” positions shown in
ABTT system display 8001 may further include an up arrow button 8146, a down arrow button 8148, a left arrow button 8150, a right arrow button 8152, and an enter button 8154. As described further herein, these buttons may assist in accessing expanded features of ABTT monitoring system 8000.
Similar to dial gauge or display 8010, bar gauge 8012 may include a high temperature limit indicator 8030, a low limit indicator 8032, and a temperature indicator 8034. Simultaneous displays of temperature in more than one type of unit, such as degrees Celsius and degrees Fahrenheit, may be provided. Alternatively, a single display of units may be provided, and units switch 8036 may be used to select the type of units displayed. As with dial gauge or display 8010, high temperature limit indicator 8030 may be in a first color, low limit indicator 8032 may be in a second color, and temperature 8034 may be in a third color, with the term color or temperature color including black and white. Temperature indicator 8034 may be associated with a bar portion 8038 that presents in a color different from an area 8040 adjacent bar portion 8038.
Digital display 8014 may also be configured to present temperature in more than one unit, or may present a single unit at a time that may be selected by units switch 8036. In order to present high and low limits, digital display 8014 may include flashing lights, changing colors, separate displayed indicators, and the like. Display 8014 also may include specialized LED (in the physical unit) or software-based specialized flashing light or lights that turn on and that are displayed on the display, and that warn about imminent danger or to guide a procedure.
In addition to the aforementioned controls and gauges or displays, ABTT system display 8001 may include elements. For example, system display 8001 may include an alarm display 8042 that flashes or changes colors when a high or low limit is reached, or when other predetermined conditions exist, such as a system fault or failure to receive a temperature signal. System display 8001 may also include an ON/OFF control or switch 8044, an interval portion 8046 with controls or switches and a display to set and display a temperature measurement interval or length of time, a START switch or control 8048 to control the start of a measurement interval or length of time, which may also act to control stop of the measurement interval or length of time, a RESET button, switch, or control 8050 to clear all controls or restore them to an unset or nominal position, and a speaker 8052 for providing audible alarms or other notifications.
System display 8001 may provide error conditions on an existing display portion, or may include a dedicated display portion.
In any of the aforementioned condition, alarm tones or signals, including spoken alerts or warnings, can be enabled to warn of these conditions as well as operator set warning levels for patient temperature.
Returning to
Temperature sensor 8002 is designed for “spot” or instantaneous readings of the SMO site, as well as temperature measurements on any skin surface. Temperature sensor 8002 is configured to be disposable. However, temperature sensor 8002 may also be configured to be sterilized at high temperature or in a liquid such as alcohol. Temperature sensor 8002 includes a generally or substantially longitudinal body 8060 that includes a tapered portion 8062 and a main body or handle portion 8064. Cable 8056a enters and is physically retained in main body 8064 at a first end of temperature sensor 8002. In the exemplary embodiment of
Temperature sensor or probe 8004, shown in
Temperature sensor 8006, shown in
LED's 8088 may be positioned in a protrusion 8092 extending from shield 8082 in a direction that is toward probe 8084. Each protrusion 8092 may be formed to direct the light output from LED's 8088 at an angle 8094 to a longitudinal axis 8096 of temperature sensor 8006 such that the light from LED's 8088 is configured to be directed slightly in front of thermistor 8086. The benefit of this configuration is that the light from LED's 8088 is configured to illuminate the ABTT area, enabling a user or operator to find the ABTT more easily in all ambient light conditions.
Temperature sensor 8008 is similar to temperature sensor 8004 in that it is intended for long-term use. Temperature sensor 8008 may be affixed directly to a subject or patient by adhesive or tape, or may be mounted, attached, or positioned to an appliance, such as a frame similar to eyeglass frames, a headband, a hat, or any head-mounted gear, thus holding the thermistor portion of temperature sensor 8008 to a patient or subject ABTT, though temperature sensor 8008 is suitable for measuring temperature in multiple locations on the body. Temperature sensor 8008 includes a thermistor 8098, which may be similar to the thermistors previously described herein, and an insulated backing pad 8100. Insulated pad 8100 may be attached to a mechanism (not shown) that provides a spring or other preload to keep thermistor 8098 in physical contact with a patient or subject's ABTT.
While the operating environments for temperature sensors are well understood, the following information is provided for guidance. Common components for the temperature sensors include the precision thermistor, and may include medical grade quick recovery polyurethane foam insulation, two layers of a white insulating foam, and adhesive backed structural insulating foam, and a protective sleeve covering the thermistor lead. All temperature sensors may incorporate a protected terminal connector. Thermistor wire leads 8056a-d are insulated with an insulating material. The thermistor is protected with an insulating coating. The final structure may be coated with another protective layer).
The support structure for the thermistor used in the sensors of
ABTT monitoring system 8000 includes a plurality of hardware elements, units, or subsystems that provide many of the functional capabilities of ABTT monitoring system 8000, an exemplary embodiment of which is shown in
ABTT monitoring system 8000 may be configured to be an electrically isolated microprocessor-based interface providing temperature readings from the attached thermistor temperature sensor to an internal or external controller. It should be understood that other readings, including blood pressure, heart rate, respiratory rate, oximetry, oxygen, carbon dioxide, concentration of molecules (e.g. glucose), blood components, and the like, that use an electrically isolated microprocessor-based interface are within the scope of the disclosure.
ABTT monitoring system 8000 may derive its power from an external computer. The operating voltage range is between 4.7 volts and 5.3 volts, with a nominal current consumption at 5.0 volts of 190 ma. ABTT monitoring system 8000 may have two different ground separations to provide a power supply with two different isolated DC-to-DC power converters. These two DC-to-DC power converters may have UL recognition per UL 1577. Alternatively, ABTT system display 8001 may include a power supply 8104 that is configured to receive external power, which is typically AC power, and to generate at least one filtered DC power for the elements, units, or subsystems of ABTT system display 8001. Power supply 8104 may include an integral power distribution system, or may supply a separate power distribution system 8106. Power supply 8104 and power distribution system 8106 provide the power required by the various elements, units, or subsystems of ABTT system display 8001. As yet another alternative, ABTT monitoring system 8000 may include batteries 8107 that supply power to power distribution 8106. Because of the moderate power consumption of ABTT monitoring, either four standard AA alkaline or four AA NiMH cells are configured to power the STM for at least 24 hours. Because such power supplies and distribution systems are generally well understood in the art, they will not be described further herein.
Although any biological parameter can be monitored according to this present disclosure, by way of illustrating one particular biological signal being monitored, ABTT system display 8001 receives a signal representing temperature from a temperature sensor via port or connector 8054. To process the signal, ABTT system display 8001 may include an amplifier 8108, an analog-to-digital (A/D) converter 8110, and a system unit controller 8112. Amplifier 8108 receives the signal from the temperature sensor and increases the strength of the signal from the temperature sensor, and may also filter the signal to remove noise. The amplified signal is sent from amplifier 8108 to A/D converter 8110, where the signal is converted to a digital format that is provided to an input of ABTT system unit controller 8112. System unit controller 8112 performs a variety of functions within ABTT system 8000.
ABTT system display 8001 may further include a non-transient memory 8114, a display controller 8116, a display 8118, an alarm controller 8120, a speaker 8122, and a plurality of panel controls 8124.
Once in system unit controller 8112, the digital temperature signal may be stored in non-transitory memory 8114, which may be removable memory, for archival purposes or for later analysis. In an exemplary embodiment, up to approximately 24 hours of data may be stored in non-transitory memory 8114 for later analysis or download to an external computer. The digital temperature signal is also provided to display controller 8116, which may be integral to ABTT system unit controller 8112, or may be a separate controller, as shown in
Returning to system unit controller 8112, the temperature signal is analyzed to determine whether the received temperature is at or under a predetermined temperature level or at or over a predetermined temperature level. If the temperature is at or above predetermined levels or limits, a signal is transmitted to an alarm controller 8120, which suitably prepares the signal to be output to various devices for alarm-related functions. For example, the signal transmitted to alarm controller may be used to initiate an audible alarm, which may include tones, vocal warnings, etc., that are provided to speaker 8122. Alarm controller 8120 may also provide a suitable signal for display to display controller 8116 or other output, such as alarm display 8042, as well as a wireless signal to a remote device, including, but not limited to, a cell phone, tablet, external computer, watch, eyeglasses, and the like.
Panel controls 8124 may include, among other controls, high limit set switch 8022, low limit set switch 8024, Wi-Fi switch 8028, units switch 8036, ON/OFF switch 8044, set interval switches that are part of set interval portion 8046, and RESET button or switch 8050. The signals from various panel controls are provided to system unit controller 8112, which responds to the signals according to their source, and as described herein. As examples, system unit controller 8112 may receive signals from high limit set switch 8022 used to establish a high temperature limit, which is translated into a position of high limit pointer 8016 and/or high temperature limit indicator 8030, either in system unit controller 8112 or in display controller 8116. The signals received from other panel controls are also suitably processed by ABTT system unit controller 8112 and used to operate the various functions of ABTT monitoring system 8000.
ABTT system display 8001 may further include a Wi-Fi or other near field communication (NFC) device 8126. Wi-Fi device 8126 may be used to communicate with the temperature sensor, with an external computer, tablet, cell phone, watch, eyeglasses, or the like, or another properly enabled device.
USB port 8026 may be used to communicate with one or more external devices, such as a computer mouse 8128, an external computer, tablet, cell phone, watch, eyeglasses, or the like 8130, or an external non-transitory memory, which may be similar to a non-transitory memory 8134 included in external computing device 8130. External computer 8130 includes an external computer controller 8132 for performing various types of analysis on temperature signal data, non-transitory memory 8134, and a computer display 8138. Additionally, external computer 8130 may provide additional functionality to ABTT monitoring system 8000.
Because ABTT monitoring system 8000 includes non-transitory memory 8114 and system unit controller 8112, if the temperature sensor, such as temperature sensor 8002, is disconnected and later reconnected, any set points and limits are configured to remain where last set. If ABTT monitoring system 8000 is shut down and restarted—the set points are configured to default to predetermined or pre-programmed levels, such as 34.0° C. for the low limit and 38° C. for the high limit. As will be described further herein, tones may be used to help establish the position of the temperature sensor. These tones, alert alarms, and other functions of ABTT monitoring system 8000 are stored in non-transitory memory, such as non-transitory memory 8114, or non-transitory memory located in one or more of the controllers of ABTT monitoring system 8000, such as ABTT system unit controller 8112, display controller 8116, or alarm controller 8120. Various functions of ABTT monitoring system 8000 are enabled during startup of ABTT monitoring system 8000.
As described previously herein, the above-description is for an exemplary embodiment of ABTT monitoring system 8000. Additional exemplary features of ABTT monitoring system 8000 are provided in the following paragraphs.
Housing 8102 may be configured to be disinfected using medical alcohol (70% concentration) without damage;
Housing 8102 may be a conventional “off-the-shelf” component or a custom-designed housing. For cost reasons, a conventional off-the-shelf component is preferred.
Housing 8102 may be configured with a detachable IV pole clamp (not shown). The pole clamp may be used to assist in routing the cable for an associated temperature sensor or for other functions.
Housing 8102 may be configured to provide access to four standard AA batteries without disassembly of housing 8102.
The portion of housing 8102 that locates display 8118 is generally considered a front panel 8158.
Front panel 8158 may include input buttons for “Left” (left arrow button 8150), “Right” (right arrow button 8152), “Up” (up arrow button 8146), “Down” (down arrow button 8148), “Enter” (enter button 8154), “Reset” (reset button 8050), and “Power” (ON/OFF switch 8044).
The buttons on front panel 8118 of housing 8102 may be configured as capacitive touch sensors.
ABTT monitoring system 8000 may be configured to include an audible alarm, which is shown as speaker 8052 in an exemplary embodiment of this disclosure.
In an exemplary embodiment, the audible alarm produces tones from 100 Hz to 6200 Hz.
In an exemplary embodiment, the amplitude of audible alarm tones may be at least 60 dB-SPL at 3.0 kHz frequency.
In an exemplary embodiment, ABTT monitoring system 8000 is configured to operate for a minimum of 24 hours on four standard NiMH AA batteries or cells (not shown) or on four standard Alkaline AA batteries or cells.
In an exemplary embodiment, ABTT monitoring system 8000 is configured not to be damaged by the insertion of NiCad AA batteries or cells; i.e., ABTT monitoring system is configured to operate without damage on NiCad AA batteries or cells and installing such does not require damaging or disassembling ABTT monitoring system 8000. More specifically, housing 8102 includes access for permit the installation of four AA batteries (not shown). Such access may be through a fastener-free panel or may be through a panel secured by one or more fasteners the principal purpose of which is to provide access to a battery bay (not shown).
In an exemplary embodiment, ABTT monitoring system 8000 is configured to be powered by an off-the-shelf medical rated power adapter.
As previously described herein, ABTT monitoring system 8000 is configured to interface with an STP or temperature sensor, such as those described herein, or any other type of sensor.
In an exemplary embodiment, a temperature sensor of ABTT monitoring system 8000, such as temperature sensors 8002, 8004, 8006, or 8008, is configured with a conventional 1OK31AM thermistor.
In an exemplary embodiment, ABTT monitoring system 8000 is configured to allow no more than 2 μA of current to flow through the temperature sensor or STP over the normal temperature sensor or STP sensing range.
In an exemplary embodiment, ABTT monitoring system 8000 is configured to use low voltage and low current. Furthermore, contact between a patient or subject and voltage and current is prevented by design. Lastly, ABTT monitoring system 8000 is configured for low electromagnetic interference susceptibility.
In an exemplary embodiment, ABTT monitoring system 8000 is configured with an ambient temperature sensor 8160. In an exemplary embodiment, ambient temperature sensor 8160 is configured to have a digital output. Alternatively, if ambient temperature sensor 8160 has an analog output, the output may be input to an A/D converter, such as A/D converter 8110. If an ambient temperature sensor is provided, in an exemplary embodiment ambient temperature sensor 8160 is configured with a resolution of at least 1.0 degree Celsius.
In an exemplary embodiment, ABTT system display 8001 and display 8118 is configured to have dimensions such that temperatures presented on display 8118 are of a size that a person with average eyesight can read the displayed temperature from 1 meter away. In another embodiment, ABTT system display 8001 is configured to conform to the readability requirements of ASTM E1112-00 section 4.4.2.2. In exemplary embodiments, display 8118 is configured with sufficient resolution to display a temperature graph with the desired temperature resolution.
In an exemplary embodiment, display 8118 is configured to have sufficient brightness to be visible in normal office, laboratory, and clinical environments, excepting direct illumination by high-intensity operating room lights or similar lights. To improve visibility in the presence of high-brightness or intensity lighting, housing 8102 may be configured to include a shield to reduce direct illumination of display 8118 by lights positioned vertically higher than ABTT monitoring system 8000.
In an exemplary embodiment, display 8118 is configured to be visible in darkened room conditions. Thus, in some embodiments display 8118 may include backlighting, side lighting, etc., to provide sufficient illumination to read display 8118. Included in such an embodiment may be appropriate lighting for bar graph or gauge 8012 and digital display 8014, if bar graph 8012 or digital display 8014 is provided separately from display 8118. For convenience of explanation, lighting may be described as “backlighting,” but in the context of this application, backlighting refers to any apparatus used to illuminate the displays described herein.
In an exemplary embodiment, display 8118 is configured to allow control of display intensity.
In an exemplary embodiment, ABTT monitoring system 8000 includes non-volatile memory 8114 for storage of temperature and other system functions. Non-volatile memory 8114 may include sufficient data storage to store at least 24 hours of 1 to 15 second temperature sensor or STP temperature readings, display 8118 characteristics, and operational parameters, as required. Furthermore, in an exemplary embodiment, non-volatile memory is configured to provide sufficient read/write cycles to allow continuous operation for at least 10 years, and is configured to provide at least one megabyte of memory more than is required by initial program implementation. Given the current state-of-the-art in non-volatile memory, the read/write speeds and space needed for ABTT monitoring system 8000 are easily met by a number of conventional technologies at a price that is effectively free in consideration of the overall anticipated cost of ABTT monitoring system 8000. Thus, a memory margin of one megabyte may easily become one gigabyte with negligible cost increase.
In an exemplary embodiment, ABTT monitoring system 8000 includes an interface that is electronically isolated for use in the field and while connected to a patient with a temperature sensor or STP. The interface may be incorporated as part of amplifier 8108, as a part of ISM 8136, as part of another component, or as an entirely separate component.
In the exemplary embodiment, ABTT monitoring system 8000 includes at least one controller, such as system unit controller 8112. System unit controller 8112 is typically a commonly available conventional controller, though it may be a custom-made controller. It is preferable that all controllers used in conjunction with ABTT monitoring system 8000 be supported by readily available cost effective development tools. It is also preferable that system unit controller 8112 have either integral or separate non-volatile memory, such as non-volatile memory 8114. Non-volatile memory 8114 may be flash based program memory or other non-volatile memories.
In an exemplary embodiment, system unit controller 8112 may be reprogrammable, either via USB port 8026, or by a connector 8156 specifically for that purpose within housing 8102. Alternatively, connector 8156 may be accessible from an external location on housing 8102, for example, on a back panel of housing 8102 that is opposite front panel 8158. In an exemplary embodiment, program memory of system unit controller 8112 is sized such that no more than approximately 50% of program memory is used by the initial software implementation. Thus, program memory is configured to have capacity for updates and upgrades, enabling each ABTT monitoring system 8000 to have a relatively long useful life.
In an exemplary embodiment, ABTT monitoring system 8000 includes a watchdog timer (not shown). The watchdog timer may be stand alone or part of system unit controller 8112. In a typical embodiment, the watchdog timer is configured to be active all the time or full time. The watchdog timer is useful in associating temperature readings with particular times, which is useful in analyzing the temperature readings.
ABTT monitoring system 8000 may include an Interface System Module (ISM) 8136, shown in at least
The circuit in interface module 8136 is double isolated from the power from an external computer or other external controller 8130 using approved power and port signal isolation circuitry. The earth ground stops at the shield of the port connector. Interface module 8136 is covered by a suitable plastic that prevents any direct connection to earth ground to anyone touching or holding the case. ISM 8136 provides much or all of the functionality of ABTT monitoring system 8000 when used in conjunction with an external computer, such as external computer 8130. Features of an exemplary embodiment of ISM 8136 may include:
Single chip port to asynchronous serial data transfer interface;
Fully integrated 1024 bit EEPROM storing device descriptors and CBUS I/O configuration;
Fully integrated port termination resistors;
Fully integrated clock generation and clock output selection;
128 byte receive buffer and 256 byte transmit buffer to allow for high data throughout;
Chip-ID feature;
Configurable CBUS I/O pins;
Transmit and receive LED drive signals;
Integrated level converter for port I/O;
Integrated +3.3V level converter for port I/O;
Fully integrated AVCC supply filtering—no external filtering required;
UART signal inversion option;
+3.3V (using external oscillator) to +5.25V (internal oscillator) Single Supply Operation;
Low operating and port suspended current;
Low bandwidth consumption;
UHC/OHCI/EHCI host controller compatible;
Post 2.0 Full Speed compatible;
−40° C. to 85° C. extended operating temperature range;
Available in compact lead-free 28 Pin SSOP and QFN-32 packages (both RoHS compliant);
Port Module Interface to RS232/RS422/RS485 Converters;
Cellular and Cordless phone data transfer cables and interfaces;
Interfacing MCU/PLD/FPGA based designs to port;
Audio and Low Bandwidth Video data transfer;
PDA to port data transfer;
MP3 Player Interface; Flash Card Reader and Writer;
Digital Camera Interface;
Hardware Modems;
Bar Code Readers;
Software and Hardware Encryption Dongles; and
Linear power regulators (LDO)-LT 1762-150 mA, Low Noise Micro-power Regulators.
While ABTT monitoring system 8000 may be configured with circuits that perform temperature analysis, software and/or firmware provide greater flexibility for operation of system 8000. Exemplary embodiments of the software are configured to perform an array of functions, as described herein. For simplicity, the software for ABTT monitoring system 8000 is described simply as system 8000 software.
In an exemplary embodiment, system 8000 software is configured to use watchdog timer.
In most exemplary embodiments, system 8000 software is configured to be implemented predominantly in a commonly used high level language.
In an exemplary embodiment, system 8000 software is configured to have a program setup mode. The program setup mode is configured to be entered on command, which may be from ABTT system display 8001, or from an external controller or computer, such as external computer 8130. The setup mode allows an option for selecting units, such as Celsius and Fahrenheit, high temperature and low temperature limits, and other adjustable parameters of ABTT monitoring system 8000, as opposed to physical switches and buttons on front panel 8158 of housing 8102. The program setup mode may be exited at any point with an appropriate command or command key, such as EXIT or END.
In an exemplary embodiment, the low temperature alarm level is adjustable between 29.0° C. and 38.0° C. in 0.1 degree increments. Also in an exemplary embodiment, the low temperature alarm level defaults to 34° C.
In an exemplary embodiment, the system 8000 software is configured to set the high temperature limit, which in an exemplary embodiment is adjustable between 35.0° C. and 40.0° C. in 0.1° C. increments. If the high temperature limit or level is reached, an alarm may sound, if sound is enabled, along with one or more visible indicators on front panel 8158 of ABTT system display 8001. In an exemplary embodiment, the high temperature limit or alarm level is configured to default to 38.5° C.
In an exemplary embodiment, system 8000 software is configured to allow setting of the amplitude or intensity of audible tones and alarms.
In an exemplary embodiment, system 8000 software is configured to set a conversion offset of ABTT monitoring system 8001, which in an exemplary embodiment is adjustable from −10.0° C. to 10.0° C. in 0.1° C. increments. Also in an exemplary embodiment, the conversion offset is configured to default to 0.0° C.
In an exemplary embodiment, system 8000 software is configured with a sensor placement mode. The sensor placement mode is entered on command, which may be from display 8118, from a switch or button on front panel 8158 of ABTT system display 8001, or from an external controller, such as external computer 8130. System 8000 software is configured to enter the sensor placement mode on command. In an exemplary embodiment, system 8000 software is configured to receive a temperature signal from a temperature sensor or probe every 250 milliseconds (ms). To conserve power, in an exemplary embodiment the system 8000 software may power the temperature sensor or probe for no more than 1 ms out of every 250 ms. The system 8000 software may be configured to acquire multiple readings from a temperature sensor or probe and to average those readings in the sensor placement mode. In an exemplary embodiment, system 8000 software may acquire and average sixteen readings from the temperature sensor or probe in the temperature placement mode. It should be apparent from the previously provided description herein that the system 8000 software is configured to display the temperature readings, averaged, instantaneous, or otherwise, in the selected display units, typically degrees Celsius or degrees Fahrenheit.
In an exemplary embodiment of the present disclosure, system 8000 software is configured to product a tone proportional to the temperature sensed on the temperature sensor or probe in the sensor placement mode. As a distinct indicator of low temperatures that would normally be considered out of range, an exemplary system 8000 software is configured to produce an audible tone of 150 Hz when the temperature signal from the temperature sensor or probe is at or below 30° C. Similarly, system 8000 software may be configured to produce an audible tone of 6000 Hz when the signal from the temperature sensor or probe is at or above 43° C. As with most modes of ABTT monitoring system 8000, system 8000 software is configured to leave the sensor placement mode upon command. Alternatively, system 8000 software may be configured to leave the sensor placement mode after three minutes.
Once the temperature sensor has been positioned or placed on the ABTT terminus, in an exemplary embodiment the system 8000 software enters an operational mode. In the operational mode, the system 8000 software is configured to receive a temperature reading at intervals, which by default may be once every 15 seconds. However, it should be understood that the reading interval can range from less than a second up to 60 seconds. To preserve system power for battery mode operation, system 8000 software may limit the time as which the temperature sensor is powered. In an exemplary embodiment, the system 8000 software may power the temperature sensor or probe in the operational mode for a maximum of 1 ms out of every 15 seconds.
In an exemplary embodiment, system 8000 software may acquire and average sixteen readings from the temperature sensor or probe in the operational mode. However, it should be understood that less than 16 readings is also within the scope of this disclosure. It should be apparent from the previously provided description herein that the system 8000 software is configured to display the temperature readings, averaged, instantaneous, or otherwise, in the selected display units, typically degrees Celsius or degrees Fahrenheit.
If ABTT monitoring system includes an ambient temperature sensor, such as temperature sensor 8160, in an exemplary embodiment, system 8000 software may be configured to read the temperature from ambient temperature sensor 8160 every 15 seconds. In another exemplary embodiment, ambient temperature may be read from temperature sensor 8160 in a range of 10 to 15 seconds. In a further exemplary embodiment, ambient temperature may be read from temperature sensor 8160 in a range of 5 to 10 seconds.
When ABTT monitoring system 8000 enters a battery powered mode, i.e., external power is not available to ABTT monitoring system 8000, the system 8000 software is configured to determine the remaining battery life periodically. In an exemplary embodiment, remaining battery life may be determined approximately once every 60 seconds.
As previously described herein, an exemplary embodiment ABTT monitoring system 8000 includes non-volatile memory. System 8000 software is configured to store each temperature sensor or probe temperature reading in non-volatile memory. However, ABTT monitoring system 8000 is not limited to storing temperature data in non-volatile memory, though such storage is preferable for making the data available for future analysis and reference purposes. In an exemplary embodiment, system 8000 software is configured to save the most recent 24 hours of temperature readings in non-volatile memory. However, ABTT monitoring system 8000 is not limited to 24 hours. In some embodiments, data may not be save in non-volatile memory at all. In other embodiments, data may be saved for days, weeks, or even longer, depending on the particular environment in which ABTT monitoring system 8000 is being used and the requirements of that environment. Data may also be saved in memory (not shown) housed in or co-located with temperature sensor 8002, 8004, 8006, or 8008.
As described herein, an exemplary embodiment ABTT monitoring system 8000 in accordance with the present disclosure includes a display 8118. System 8000 software is configured to display currently sensed temperature sensor or probe temperature in the selected display units, typically degrees Celsius, degrees Fahrenheit, or both. In an exemplary embodiment, display of temperature may be in 0.1 degree increments.
System 8000 software is also typically configured to display the ambient temperature, which may be on ambient temperature display 8164, received from ambient temperature sensor 8160 or from elsewhere, in the currently selected display units, though the units for the ambient temperature display may be selected independently of other temperature displays on ABTT system display 8001. If system 8000 software is configured to display ambient temperature, the resolution of the ambient temperature is at least 1 degree, with 0.1 degree being preferable.
In an exemplary embodiment, system 8000 software is configured to display the remaining battery life on display 8118. Such display may be on battery life display 8162.
As described herein, the displays of ABTT monitoring system 8000 may include backlighting, side lighting, or other lighting to enable reading of the various displays presented by ABTT system display 8001. To conserve power, system 8000 software is configured to turn off the backlight after a predetermined time after a new reading or alarm is displayed. Such a power saving mode may be a standard operating mode, or may be entered when a low battery condition is detected.
Alarms have been previously described herein. System 8000 software is configured to provide a visible alarm on ABTT system display 8001, such as by flashing the display, or presenting an alarm signal on a separate display, such as display 8042. Alarms may also be audible, and system 8000 software is configured to enable or disable audible alarms, prior to an alarm condition or after the alarm condition. If an alarm condition exists and audible tones are present, the audible tones may be disabled by pressing reset button 8050 once, which permits displayed alarms to continue. Pressing reset button 8050 a second time resets all displayed alarms to a non-alarm condition. When an audible alarm is enabled, such alarm may be by voice, which in an exemplary embodiment may present, for example, a vocal alarm indicating the precise nature of the alarm, such as: “Warning! Over-temperature condition detected”; “Warning! Under temperature condition detected”; “Fault detected. The temperature probe appears disconnected or malfunctioning”; etc. In another exemplary embodiment, the alarm may be an audible tone with a frequency of at least 3000 Hz. The alarm tone may be configured to alternate between a high tone and an off tone, or lower tone, or the alarm tone may be matched to a particular alarm condition.
If the system 8000 software detects that the temperature sensor or probe has reached or exceeded the high temperature limit, enabled alarms, display and audible, are configured to operate. Alarm display 8042 may alternate between “ALARM” and “HIGH TEMP,” or other, similar indication, to indicate that the high temperature limit has been reached. Similarly, if the system 8000 software detects that the temperature sensor or probe has reached or fallen below the low temperature limit, enabled alarms, display and audible, are configured to operate. Alarm display 8042 may alternate between “ALARM” and “LOW TEMP,” or other, similar indication, to indicate that the low temperature limit has been reached.
If system 8000 software detects a fault in ABTT monitoring system 8000 that prevents safe and accurate temperature readings from the temperature sensor, alarm display 8042 may alternate between “ALARM” and “ERR.” Similarly, if battery life is 60 minutes or less, or there is a malfunction of the battery system, system 8000 software may display “ALARM” alternating with “BATT.” If system 8000 software is able to present a temperature reading in any alarm condition, system 8000 software is configured to continue to do so even while presenting alarm indications.
ABTT monitoring system 8000 includes features to control the function of the various displays. In an exemplary embodiment, adjustment and memory of adjustment of display intensity, contrast, color balance and/or correction, size, position, sharpness, etc., may be provided, in addition to a reset button that restores all display-related settings to factory default settings.
In an exemplary embodiment, ABTT system display 8001 may include a graphing mode. Referring to
In an exemplary embodiment, system 8000 software is configured to display alarm events, such as alarm event 8178, on graphing display 8166. By selecting or touching alarm event 8178, time, date, and type of alarm is presented in a box (not shown) overlaid on graphing display 8166. The alarm information is hidden after a predetermined period, such as 3 seconds, but may also be hidden by clicking on the alarm information box while it is displayed.
In an exemplary embodiment, system 8000 software is organized as a software control loop. The software control loop is configured to place ABTT monitoring system 8000 in a low power state when no activities are pending. The software control loop is configured to be triggered by interrupt events. The software control loop is configured to call a display screen update routine on every iteration to provide updates for at least display 8118 and digital display 8014. The software control loop is configured to call port support on every iteration.
When a port is active, i.e., when data is available, the software control loop is configured to call the data transfer routine on every iteration. The software control loop is configured to call the touch switch routines every one tenth of a second; i.e., displayed or soft switches are read approximately every one tenth of a second. When any display screen, except a startup screen (not shown) or a probe setup screen (not shown), is active, the software control loop is configured to initiate a temperature read process every fifteen seconds. The temperature read process is defined as a process where power is provided to a temperature sensor or probe, unless power is already applied, and temperature is acquired over predetermined period for a predetermined number of readings.
During any process where temperature is read, including a mode where the ABTT is located and the temperature read process, when any display screen except the startup screen (not shown) or probe setup screen is active, the software control loop is configured to store the read temperature. In an exemplary embodiment, when the probe setup screen is active, the software control loop is configured to initiate the temperature read process every one quarter second.
The software control loop is configured to send stored patient temperature data when requested by the port host.
The software control loop is configured to call a battery monitor routine one per minute.
In an exemplary embodiment, system 8000 software is configured to use an interrupt based hardware timer to time STM events. The system 8000 software timer interrupt routine is configured to set flags indicating predetermined time intervals have passed. In exemplary embodiments, flags are set at one tenth second, one quarter second, one second, fifteen seconds, and one minute. In addition, the system 8000 software timer interrupt routine is configured to process timer subsystem timers.
As noted herein, ABTT monitor system 8000 includes one or more ports or connectors to interface with external devices, for example, external computer 8130. In order to communicate with such devices, in an exemplary embodiment system 8000 software is configured to include port background routines. Such port background routines are configured to be interrupt driven. Furthermore, port background routines are configured to handle all handshakes with external host devices. In addition, port background routines are configured to provide for data sent to the host device to be the system 8000 software control loop. Still further, port background routines are configured to send data from the system 8000 software control loop to the host device.
As described herein, ABTT monitoring system 8000 may include one or more soft buttons or switches, which are displayed buttons that are actuated by touch, proximity, mouse control, light pen, etc. In an exemplary embodiment, the system 8000 software is configured to read touch button values approximately every second, or less. To minimize power consumption and overly sensitive response, touch switch or touch button average values are updated every one reading when the touch button or switch is not touched. In an exemplary embodiment, if a touch button reading exceeds the touch button average for three consecutive readings, then system 8000 software is configured to consider a touch to have occurred. Conversely, if a touch button or touch switch reading is below the touch button average for three consecutive reading, the system 8000 software is configured to consider that a touch has not occurred.
As described herein, ABTT monitoring system 8000 may include a battery monitor. In an exemplary embodiment, the battery monitor of system 8000 software is configured to: check battery status once per minute; estimate remaining battery life; and to set a battery alarm flag when remaining battery life drops below 60 minutes. The battery alarm flag may then be used by system 8000 software to activate ABTT monitoring system 8000 alarms, including alarm display 8042 and the audible alarm.
Though ABTT monitoring system 8000 may include physical buttons, many or even all such buttons may be connected through the system 8000 software. Accordingly, this discussion incorporates mechanical and soft or displayed switches.
When ABTT monitoring system 8000 is in a power off state or condition, the power button or ON/OFF switch 8044, when the ON position is selected, is configured to connect power to ABTT monitoring system 8000 to operate system 8000 or turn system 8000 to a power on or operating condition, assuming a valid power source is available. Conversely, if ON/OFF switch 8044 is moved from the ON position to the OFF position, then power is removed from the internal devices, components, and elements of ABTT monitoring system 8000, and system 8000 assumes a power off condition.
For the following discussion of buttons and switches, the term “any button” generally refers to any button except the power button and as otherwise noted. Generally, ABTT monitoring system 8000 is configured such that pressing any button at any level causes an audible “click.” This condition exists for mechanical switches and soft switches. Pressing any button while display 8118 is active and with any backlighting, side lighting, or front light inactive causes any such type of lighting to activate with no other action.
ABTT monitoring system 8000 is configured to include a temperature read process 8179, shown in
At a start process 8180, ABTT monitoring system 8000 is set to an on or powered condition. Once power is provided to ABTT monitoring system 8000, all systems are set to factory default conditions or a previously set and saved condition, if such is provided. Included is resetting all storage to a zero or null condition, and all comparators to a null or zero condition. Control then passes from start process 8180 to a valid power decision process 8182.
In valid power decision process 8182, ABTT monitoring system 8000 determines that valid power is available. The determination of valid power may be made in power distribution hardware unit 8106. If valid power is available, then a valid power condition is determined, and power is automatically provided through power distribution 8106 to the systems, elements, and components of ABTT monitoring system 8000. If valid power is not available, control passes from valid power decision process 8182 to an end process 8184. In some embodiments, digital display 8014 may indicate NOPWR, indicating valid power is not available. If valid power is available, control passes from valid power decision process 8182 to a power ABTT monitoring system process 8186.
In process 8186, power is provided to various systems, components, and elements of ABTT monitoring system 8000, except for portions of ABTT monitoring system 8000 that are not yet required to be powered or are optionally operated. Such optional systems may include Wi-Fi or near field communication unit 8126 and the temperature sensor. Once power ABTT monitoring system process 8186 is complete, control passes from power ABTT monitoring system process 8186 to an initiate system software process 8188.
After power is provided to all portions of ABTT monitoring system 8000, controller 8112 begins operating and initiates system 8000 software to perform the functions of ABTT monitoring system 8000 in initiate system software process 8188. Once system 8000 software is operational, control passes from initiate system software process 8188 to a power temperature sensor process 8190.
In power temperature sensor process 8190, power is provided to the temperature sensor. Control then passes from process 8190 to a receive temperature readings process 8192.
In receive temperature sensor readings process 8192, controller 8112 receives a predetermined number of temperature readings from A/D converter 8110. In an exemplary embodiment, the number of temperature readings may be sixteen. Once the predetermined number of temperature readings has been received by controller 8112, control passes from receive temperature sensor readings process 8192 to a temperature sensor power off process 8194, where power to the temperature sensor is removed. Control then passes from process 8194 to an average temperature process 8196, where the average temperature is calculated from the predetermined number of readings. Control then passes from average temperature process 8196 to a determine temperature sensor or probe condition process 8198.
In process 8198, the average temperature is converted to a value using a translation table. The purpose of the translation table is to substitute a digital value for a measured probe condition. If the translated average reading is 0x0000, then process 8198 substitutes a PROBE_SHORTED value for the reading. If the translated average reading is 0xfff, then process 8198 substitutes a PROBE_OPEN value for the reading. If the translated average reading is below the lowest translation table value available, then process 8198 substitutes a PROBE_LOW value for the reading. If the translated average reading is above the highest translation table reading, then process 8198 substitutes a PROBE_HIGH value for the reading. Once probe condition process 8198 is complete, control passes from process 8198 to a sensor error decision process 8200.
If any error condition is returned from process 8198, then an error condition exists, and control passes from sensor error decision process 8200 to a display error code process 8202. In process 8202, an error is displayed, which may be, for example, on digital display 8014. Exemplary error codes are described herein. Once process 8202 is complete, control passes to a valid temperature available decision process 8204.
In valid temperature decision process 8204, a determination is made as to whether a valid temperature exists, such as a temperature below a lower limit, above, a lower limit, or other valid temperature, even in the presence of an error. If a valid temperature is not available, control passes to an end process 8206 and temperature read process 8179 ends. If a valid temperature is available, control passes to a display patient temperature process 8208, which is also where control passes from sensor error decision process 8200 if no sensor error condition exists.
In display patient temperature process 8208, the average temperature obtained from average temperature process 8196 is displayed on one or more portions of ABTT system display 8001, such as dial gauge 8010, bar graph or gauge 8012, and digital display 8014. Once the average temperature is displayed, control passes to a new temperature decision process 8210.
In new temperature decision process 8210, ABTT monitoring system determines whether another temperature is desired. Such a determination may be made automatically if a timeout situation has not occurred, or if temperature readings differentiate from ambient by a predetermined amount. If temperature read process 8179 determines that additional temperature readings are desired, control passes from new temperature decision process 8210 to receive temperature readings process 8192, described herein. Alternatively, if additional temperature readings no longer appear needed, then control passes from new temperature decision process 8210 to an end process 8212, where temperature read process 8179 ends.
Though temperature read process 8179 is described in terms of a power off condition of ABTT monitoring system 8000, as long as system 8000 remains on, controller 8112 periodically tests for the presence of a temperature sensor at predetermined intervals and for temperature changes that differentiate from ambient. If such changes are detected, temperature read process 8179 is initiated again, though temperature read process 8179 is configured to recognize that processes 8180 to 8188 have already been accomplished, thus control is configured to immediately pass to power temperature sensor process 8190, where temperature read process 8179 is configured to continue as previously described.
In an exemplary embodiment, system 8000 software is configured to include an ambient temperature read process. Reading ambient temperature begins by turning power on to ambient temperature sensor 8160. Once ambient temperature sensor 8160 is properly powered, signals from ambient temperature sensor representing the ambient temperature are provided to system controller 8112. Once the ambient temperature is read, power to ambient temperature sensor 8160 is turned off.
The display screens described herein are one of the easiest and most useful ways to present data acquired by ABTT monitoring system 8000. In all discussions involving displays, it should be understood that while displayed functions are sometimes described in terms of the display, all display-related functions are driven by a controller, which includes system 8000 software. Accordingly, in most cases the described actions and features are the result of system 8000 software. When power is applied to ABTT monitoring system 8000, display 8118 is configured to initially display a startup screen while various system elements, including system 8000 software, such as a logo showing ABTT, for Abreu Brain Thermal Tunnel. This initial screen may also be configured to display a part number and version for the system 8000 software. After a period, which is determined by the time it takes to initialize all systems fully, the initial startup screen is replaced by a main display screen, such as that shown in
As shown in
In an exemplary embodiment, the system 8000 software is configured so that the display of the most recent temperature data blinks when the display is being updated.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to display the most recent patient temperature on the main display screen as a numerical value.
In the exemplary embodiments presented herein, patient or subject temperature is displayed in the currently selected unit of measure.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to blink a low battery icon on the main display screen at one second intervals when a low battery alarm condition exists.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to blink an audible alarm disable icon on the main display screen at one second intervals when the audible alarm is disabled.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to clear the highest priority alarm when reset button 8050 is touched and released within two seconds.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to toggle the audible alarm flag when reset button 8050 is touched for two seconds or longer.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to toggle the display unit of measure flag when enter button 8154 is touched and released within two seconds.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to move to an option select screen when the enter button is touched for two seconds or longer.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to cause the backlight intensity to increase by 10% when down arrow button 8148 is touched and released.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured not to cause the backlight intensity to increase above 100%.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to cause the backlight intensity to decrease by 10% when down arrow button 8148 is touched and released.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured not to cause the backlight intensity to decrease below 0%.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to cause the display contrast to increase by 10% when left arrow button 8150 is touched and released.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured not to increase the display contrast above 100%.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to cause the display contrast to decrease by 10% when right arrow button 8152 is touched and released within two seconds.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured not to decrease the LCD Contrast below 0%.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to graph display screen 8166 when right arrow button 8152 is touched for two seconds or longer.
In an exemplary embodiment, while the main display screen is displayed, system 8000 software is configured to move to a temperature sensor setup display screen when enter button 8154 and reset button 8050 are touched simultaneously for two seconds or longer.
In an exemplary embodiment, ABTT monitoring system 8000 includes an option selection screen. The option select screen is configured to display an option for selecting the temperature sensor setup screen.
In an exemplary embodiment, the option select screen is configured to display an option for selecting a clear patient data screen.
In an exemplary embodiment, the option select screen is configured to display an option for selecting a low limit alarm edit screen.
In an exemplary embodiment, the option select screen is configured to display an option for selecting a high limit alarm edit screen.
In an exemplary embodiment, the option select screen is configured to display an option for selecting an audible alarm level screen.
In an exemplary embodiment, the option select screen is configured to display an option for selecting a backlight timer edit screen.
In an exemplary embodiment, while in the option select screen, system 8000 software is configured to move to the main display screen when reset button 8154 is touched and released.
In an exemplary embodiment, while in the option select screen, system 8000 software is configured to move to the currently selected option when enter button 8154 is touched and released.
In an exemplary embodiment, while in the option select screen, system 8000 software is configured to display move the currently selected option up one when up arrow button 8146 is touched and released.
In an exemplary embodiment, while in the option select screen, system 8000 software is configured to move the currently selection option to the bottom-most option when up arrow button 8146 is touched and released when the top-most option is currently selected.
In an exemplary embodiment, while in the option select screen, system 8000 software configured to move the currently selected option down one when down arrow button 8148 is touched and released.
In an exemplary embodiment, while in the option select screen, system 8000 software is configured to move the currently selected option to the top-most option when down arrow button 8148 is touched and released and the bottom-most option is currently selected.
In an exemplary embodiment, the System 8000 software is configured to include a temperature sensor setup screen.
In an exemplary embodiment, the temperature sensor setup screen is configured to display numerically the most recent patient or subject temperature.
In an exemplary embodiment, the temperature sensor setup screen is configured to display continuously the most recent patient or subject temperature date.
In an exemplary embodiment, the temperature sensor setup screen is configured to display “PS” for patient or subject temperature data with a value of PROBE_SHORTED.
In an exemplary embodiment, the temperature sensor setup screen is configured to display “NP” for patient or subject temperature data with a value of PROBE_OPEN.
In an exemplary embodiment, the temperature sensor setup screen is configured to display “Ur” for patient or temperature data with a value of PROBE_LOW.
In an exemplary embodiment, the temperature sensor setup screen is configured to display “Or” for patient or subject temperature data with a value of PROBE_HIGH.
In an exemplary embodiment, the temperature sensor setup screen is configured to blink the most recent temperature data once per second to show it is being updated.
In an exemplary embodiment, the temperature sensor setup screen is configured to display graphically the most recent patient temperature on the main display screen as a numerical value.
In an exemplary embodiment, the temperature sensor setup screen is configured to display patient or subject temperature in the currently selected unit of measure.
In an exemplary embodiment, while in the temperature sensor setup screen, system 8000 software is configured to move to a clear patient data screen when reset button is touched and released.
In an exemplary embodiment, while in the temperature sensor setup screen, system 8000 software is configured to move to the main display screen when the enter button is touched and released.
As described herein, an exemplary embodiment system 8000 software is configured to include a clear patient data screen. This feature is important for patient privacy. In an exemplary embodiment, to initiate the clear patient data screen, an authorizing identification or ID may need to be entered. In another exemplary embodiment, a patient or subject identification or ID may need entered, either in addition to an authorizing identification, or in place of the authorizing identification.
In an exemplary embodiment, the clear patient data screen is configured to display the phrase “Clear Patient Data? Reset=Yes, Enter=No.” While in the clear patient data screen, system 8000 software is configured to clear stored patient data when reset button 8050 is touched and released, after which the patient data cleared screen is configured to display the phrase “Patient Data Cleared.” While in the clear patient data screen, system 8000 software is configured to move to the patient data cleared screen when reset button is touched and released.
In an exemplary embodiment, while the clear patient data screen is displayed the system 8000 software is configured to move to the main display screen when enter button 8154 is touched and released.
While the patient data screen is displayed, system 8000 software is configured to move to the main display screen after a five second interval. Furthermore, the system 8000 software is configured to move or transition from the patient data cleared screen to the main display screen if any button on ABTT system display 8001 is touched.
As yet another options screen, in an exemplary embodiment, system 8000 software is configured to provide a low limit alarm edit screen.
The low limit alarm edit screen is configured to show the current value of the low limit alarm on entry into the low limit alarm edit screen, and the value displayed is configured to be in the selected display units of measure.
The low limit alarm edit screen is configured to display the value of the low limit alarm in the currently selected display units of measure.
While in the low limit alarm edit screen, system 8000 software is configured to increment the edited low limit alarm by 0.1 degree when up arrow button 8146 is touched and released.
While in the low limit alarm edit screen, system 8000 software is configured not to increment the edited low limit alarm above 38.0 degrees Celsius or above 100.4 degrees Fahrenheit.
While in the low limit alarm edit screen, system 8000 software is configured to decrement the edited low limit alarm by 0.1 degrees when down arrow button 8148 is touched and released.
While in the low limit alarm edit screen, system 8000 software is configured not to decrement the edited low limit alarm below 29.0 degrees Celsius or below 84.2 degrees Fahrenheit.
While in the low limit alarm edit screen, system 8000 software is configured to set the low limit alarm to the edited low limit alarm value when enter button 8154 is touched and released.
The system 8000 software is configured to move from the low limit alarm edit screen to the option select screen when reset button 8154 is touched for less than two seconds and released while the low limit alarm is equal to the edited low limit alarm.
The system 8000 software is configured to return the edited low limit alarm to its low limit alarm value when reset button 8050 is touched for less than two seconds and released while the low limit alarm is not equal to the edited low limit alarm.
While in the low limit alarm edit screen, the system 8000 software is configured to set the edited low limit alarm to the default value of 34.0 degrees Celsius when reset button 8050 is touched and held for two seconds or more.
While in the low limit alarm edit screen, the system 8000 software is configured to set the edited low limit alarm to the default value of 93.2 degrees Fahrenheit when reset button 8050 is touched and held for two seconds or more.
As yet another options screen, in an exemplary embodiment, system 8000 software is configured to provide a high limit alarm edit screen.
The high limit alarm edit screen is configured to show the current value of the high limit alarm on entry into the high limit alarm edit screen, and the value displayed is configured to be in the selected display units of measure.
The high limit alarm edit screen is configured to display the value of the high limit alarm in the currently selected display units of measure.
While in the high limit alarm edit screen, system 8000 software is configured to increment the edited high limit alarm by 0.1 degree when up arrow button 8146 is touched and released.
While in the high limit alarm edit screen, system 8000 software is configured not to increment the edited high limit alarm above 40.0 degrees Celsius or above 104.0 degrees Fahrenheit.
While in the high limit alarm edit screen, system 8000 software is configured to decrement the edited high limit alarm by 0.1 degrees when down arrow button 8148 is touched and released.
While in the high limit alarm edit screen, system 8000 software is configured not to decrement the edited high limit alarm below 35.0 degrees Celsius or below 95.0 degrees Fahrenheit.
While in the high limit alarm edit screen, system 8000 software is configured to set the high limit alarm to the edited high limit alarm value when enter button 8154 is touched and released.
The system 8000 software is configured to move from the high limit alarm edit screen to the option select screen when reset button 8154 is touched for less than two seconds and released while the high limit alarm is equal to the edited high limit alarm.
The system 8000 software is configured to return the edited high limit alarm to its high limit alarm value when reset button 8050 is touched for less than two seconds and released while the high limit alarm is not equal to the edited high limit alarm.
While in the high limit alarm edit screen, the system 8000 software is configured to set the edited high limit alarm to the default value of 38.5 degrees Celsius when reset button 8050 is touched and held for two seconds or more.
While in the high limit alarm edit screen, the system 8000 software is configured to set the edited high limit alarm to the default value of 101.3 degrees Fahrenheit when reset button 8050 is touched and held for two seconds or more.
In an exemplary embodiment, yet another of the options screens is the audible alarm level edit screen. Upon entry to the audible alarm level edit screen, system 8000 software is configured to display on the audible alarm level edit screen the current audible alarm level in percent of maximum.
While in the audible alarm level edit screen, system 8000 software is configured to increment the edited audible alarm level by 5% when the up arrow button 8146 is touched and released.
While in the audible alarm level edit screen, system 8000 software is configured not to increment the edited audible alarm level above 100%.
While in the audible alarm level edit screen, system 8000 software is configured to decrement the edited audible alarm level by 5% when down arrow button 8148 is touched and released.
While in the audible alarm level edit screen, system 8000 software is configured not to decrement the edited audible alarm level below 10%.
While in the audible alarm level edit screen, system 8000 software is configured to set the audible alarm level to the edited audible alarm level when enter button 8154 is touched and released.
While in the audible alarm level edit screen, system 8000 software is configured to move to the option select screen when reset button 8050 is touched for less than two seconds and released while the audible alarm level is equal to the edited audible alarm level.
While in the audible alarm level edit screen, system 8000 software is configured to set the edited audible alarm level to the audible alarm level when reset button is touched for less than two seconds and released while the audible alarm level is not equal to the edited audible alarm level.
While in the audible alarm level edit screen, system 8000 software is configured to set the edited audible alarm level to the default value of 50% when reset button 8050 is touched and held for two seconds or more.
In an exemplary embodiment, yet another of the options screens is the backlight timer edit screen. While in the backlight timer edit screen, system 8000 software is configured to set the edited backlight timer to the default value of 3 seconds when reset button 8050 is touched and held for two seconds or more.
While in the backlight timer edit screen, system 8000 software is configured so that upon entry the current value of the backlight timer is displayed.
While in the backlight timer edit screen, system 8000 software is configured to increment the edited backlight timer by 1 second when up arrow button 8146 is touched and released.
While in the backlight timer edit screen, system 8000 software is configured not to increment the edited backlight timer above 60 seconds.
While in the backlight timer edit screen, system 8000 software is configured to decrement the edited backlight timer by 1 second when down arrow button 8148 is touched and released.
While in the backlight timer edit screen, system 8000 software is configured not to decrement the edited backlight timer below 0 seconds.
While in the backlight timer edit screen, system 8000 software is configured to set the backlight timer to the edited backlight timer value when enter button 8154 is touched and released.
While in the backlight timer edit screen, system 8000 software is configured to move from the backlight timer edit screen to the Option Select Screen when reset button 8050 is touched for less than two seconds and released while the backlight timer is equal to the edited backlight timer.
While in the backlight timer edit screen, system 8000 software is configured to return the edited backlight timer to its currently saved value when reset button 8050 is touched for less than two seconds and released while the backlight timer is not equal to the edited backlight timer.
While in the backlight timer edit screen, system 8000 software is configured to set the edited backlight timer to the default value of 3 seconds when reset button 8050 is touched and held for two seconds or more.
As previously described, and shown in
Upon entry into graphing display 8166, system 8000 software is configured to display the previous four hours of patient or subject temperature, if available.
While in graphing display 8166, system 8000 software is configured to display current patient or subject temperature data along with the highest and lowest temperature in what may be described as a high-low graph.
While in graphing display 8166, system 8000 software is configured to display four data points in each entry of the high-low graph.
While in graphing display 8166, in an exemplary embodiment system 8000 software is configured to display graph start time relative to current time for the currently displayed graph.
While in graphing display 8166, system 8000 software is configured to display graph stop time relative to current time for the currently displayed graph.
While in graphing display 8166, system 8000 software is configured to move the currently displayed graph four hours later when right arrow button 8152 is touched and release.
While in graphing display 8166, system 8000 software is configured to move the currently displayed graph to the most recent four hours when enter button 8154 is touched and released.
While in graphing display 8166, system 8000 software is configured to move to the main display screen when reset button 8050 is touched and released.
As discussed herein, in an exemplary embodiment display 8118 and 8014 are configured to include lighting to improve the readability of those displays. Such lighting may be from backlighting, side lighting, front lighting, etc. For the sake of simplicity and convenience, all such display lighting is described as backlighting herein, though it should be understood that the term backlighting covers any type of display lighting, unless otherwise noted.
Exemplary embodiment backlighting is configured to operate at the currently selected contrast.
Exemplary embodiment backlighting is configured to be off when backlight level is zero.
Exemplary embodiment backlighting is configured to operate at the selected or set backlight level while active.
Exemplary embodiment backlighting is configured to be continuously active in any display screen except the main display screen. This configuration is possible because all screens except the main display screen are kept on for a limited period.
Exemplary embodiment backlighting is configured to operate as follows in the Main Display Screen: backlighting is continuously active in the main display screen while the backlight timer value is zero; when any button is touched in the main display screen the backlight will be activated for backlight timer time; and when the temperature display is updated backlight will be active for backlight timer time while the backlight timer time is less than 15 seconds.
The operation of ABTT monitoring system 8000 and ISM 8136 may have many different exemplary modes and conditions. The operations described herein are examples of the typical operations of ABTT monitoring system 8000 and ISM 8136, with differences between the systems identified as needed.
For ABTT monitoring system 8000, simply move ON/OFF switch 8044 from the OFF position to the ON position. ABTT monitoring system 8000 will initialize, and predetermined limits will be uploaded to system unit controller 8112 from non-transitory memory 8114. Typically, ABTT monitoring system 8000 will initialize or begin operation in a default state, which includes Wi-Fi off, interval set to zero or off, and thus temperature readings will be continuous, and units of measure set to degrees Celsius for the digital display. In the exemplary embodiment shown in
To initiate ISM 8136, connect USB port 8053 of ISM 8136 to a port of external computer 8130. Follow the “Found New Hardware” instructions presented on display 8138 of external computer 8130. Interface module 8136 will show up in the device manager of external computer 8130 as an Interface Module, which in the exemplary embodiment is named the Abreu ABTT 3.1.
Double click the Abreu 3.1 icon on the desktop to start the program. Attach any of the temperature sensors disclosed herein, such as temperature sensor 8002, 8004, 8006, or 8008, to ISM 8136. Computer display 8138 will display the temperature of the probe.
For both ABTT monitoring system 8000 and ISM 8136, a tone proportional to temperature will help the operator locate the SMO site of the ABTT, with a higher temperature indicated by a higher pitch tone (e.g., see Table 2). The tone can be disabled by un-checking the “Sound” box provided on display 8138 of computer 8130. Alarm limits can be set by clicking on the “arrow” buttons (not shown) provided on computer display 8138 that mimic the functionality of high limit switch 8022 and low limit switch 8024. Alert warning sounds can be turned off by un-checking the “Alerts” box.
The “up” and “down” arrows allow changing the alarm set points. If the program is restarted or is reset, these settings will revert to the default setting of 34.0° C. and 38.5° C., which are also the default setting for ABTT monitoring system 8000. The temperature will be displayed digitally in the upper right of display 8138 unless an error condition exist, in which case a code will indicate the error, such as codes “NC,” “NP,” “PS,” “Ur,” or “Or,” previously described herein in conjunction with digital display 8014 of ABTT monitoring system 8000.
Readings from ISM 8136 presented on display 8138 are provided frequently, at least two per second, as are readings on the various temperatures displayed on ABTT system display 8001. The rapid rate of readings enables the operator to best place the temperature probe as quickly as possible on SMO site. A tone mode is entered by depressing the “Sound” box. The displayed patient temperature will update rapidly, allowing the operator to reposition the sensor for the optimum reading, with the highest reading yielding the highest pitch. As the temperature of the sensor rises above the lower limit, a continuous tone proportional to temperature will be heard emanating from the computer. This sound feedback will help the operator easily locate the desired contact position for the sensor. Table 2 shows the correlation between temperature and sound frequency. While it is typical for the ABTT terminus to be higher temperature than surrounding skin, under certain conditions, the ABTT terminus may be cooler than surrounding skin temperature. A trained operator will recognize this situation immediately because the sound from temperature of the surrounding skin will be higher pitch than the ABTT location, which will be lower. It should be understood that the audio correlation disclosed herein associated with the temperature levels can be used with another biological parameter, in which the level of the parameter is associated with a particular audio frequency, said parameters including, but not limited to, heart rate, blood pressure, respiratory rate, oxygen levels, oximetry, blood gases, and analytes such as glucose and the like.
Once the ABTT has been located, and displayed temperature values on either ABTT system display 8001 or display 8138 no longer fluctuate, the sensor has stabilized and the displayed temperature is the measured temperature. Depending on the thermistor being used, e.g., thermistor 8066, 8074, 8086, or 8098, the response time may vary. The greater the mass of the sensor, the longer the response time since thermal equilibrium must be established with the environment, either ambient, the ABTT, or elsewhere.
As shown in
As previously noted herein, temperature sensor 8004 is configured to be a one-use or disposable temperature sensor or probe. Temperature sensor 8004 may come with an adhesive layer 8142, which may be protected by a cover. After locating the SMO site, remove the cover of adhesive layer 8142 and press adhesive layer 8142 against the patient's forehead in the approximate orientation shown in
Longitudinally extending temperature sensors, such as temperature sensors 8002 and 8006, shown in
To cease operation of ABTT monitoring system 8000, ON/OFF switch 8044 may be moved from the ON position to the OFF position. For operation with external computer 8130, a displayed “STOP” or “OFF” button may be presented and selected, either by mouse 8128, touch, if display 8138 of external computer 8130 is provided with a touch screen, by a shortcut key (not shown), or through other devices or configurations.
Once system 8000 initialization has been completed, system 8000 firmware operates entirely in an infinite loop. No interrupts are used or enabled. The mail loop waits for input from the UART or for calibration pin to be pulled low. The mail loop also checks for and corrects UART RX overflow errors. If the calibration input is pulled low new calibration constants are obtained from A/D converter inputs and stored in EEPROM. If a valid command is read from the UART, the firmware executes the corresponding command. Commands include sampling A/D converter inputs, printing version information, and retrieving calibration constants. Each time the A/D converter is sampled at a high level, the firmware computes the average of a predetermined number of successive temperature readings, which in an exemplary embodiment may be 16 successive measurements with the A/D converter. Thermistor drive voltages are disabled until a command is given to measure one of the inputs. Once the measurement is complete (the predetermined number of individual measurements, e.g., 16 individual measurements, plus a short delay) temperature sensor or thermistor drive voltage is once again disabled.
ABTT monitoring system 8000 uses a common port for power, which is 5.0V DC. Following are electrical features of ABTT monitoring system 8000 in an exemplary embodiment.
The maximum patient leakage current is 27 micro-amps.
The maximum patient leakage current is 32 micro-amps.
The maximum patient leakage current is 28 micro-amps.
Patient auxiliary current measurement would require a double fault assumption, therefore it is not applicable.
The maximum touch current of the temperature sensor is so minute it is insignificant (less than 3 micro-amps).
ABTT monitoring system 8000 does not use a protective earth connection.
In addition to protective circuitry design, the means of patient protection are two coats of electrical insulation on the thermistor. The thermistor is soldered to silver/copper wires, then a thin layer of insulation is applied to the thermistor and the soldered connections. In final assembly, the thermistor is attached to the finger, pen, or applique (the longitudinal body of the temperature sensor) and a thick layer of appropriate adhesive is placed over the thermistor, providing voltage isolation.
In an exemplary embodiment, a temperature sensor is connected directly to a personal computer, which then functions as the power supply.
In an exemplary embodiment, the working voltage of the thermistor is 3.3V DC.
The air clearance for MOOP is around the screws which hold the box together, which creates a static distance if the device were deformed or movement of parts.
The screws in ABTT monitoring system 8000 have been isolated with and air gap around them.
Regardless of whether a personal computer serves as the controller or ABTT monitoring system 8000, if a temperature sensor is detached from the PC or ABTT monitoring system 8000, and then reattached, operation of the system continues automatically.
Healthcare care costs are rapidly increasing and the ability to have an at home medical monitoring devices are onerous. Furthermore, as described in U.S. Pat. No. 7,187,960 to Applicant, Applicant has conquered what may the last frontier for automation of patient monitoring. With the exception of temperature, all other vital signs can currently be monitored continuously, noninvasively, and automatically. Now, with the discovery of the Abreu Brain Thermal Tunnel (ABTT), described herein, all vital signs can be monitored continuously and noninvasively. For a person to buy all the currently available biological monitoring devices, e.g., EKG, EEG, blood pressure, heart rate, etc., would be very expensive. Therefore, the vast majority of the population is not able to take advantage of such medical advances. The inventions of the present disclosure provide a heretofore unrealized opportunity to provide an affordable biological parameter monitoring system for home use. The present discloses describes new household appliances and household electronics designed for continuous and noninvasive monitoring of biological parameters, referred herein as Medical Grade Household Appliances and Electronics (MGHAE). Therefore, when people buy appliances in the future, they may also be receiving a medical device or devices or a medical system or systems. The present disclosure provides new appliances with medical grade configuration and medical grade circuitry, electronics, and ports. Nowadays, a variety of household appliances and electronics have electronic circuitry, ports, and displays which sit idle and have no medical function. The present disclosure maximizes and optimizes the use of such displays, circuitry, memory, and ports by creating medical grade devices while allowing standard features and function of the household device to function in a regular or normal manner. More importantly, the features of the present disclosure allow people to monitor their biological parameters while at home or at work by being connected to a MGHAE of the present disclosure. The monitoring systems disclosed herein for monitoring temperature and its associated electronics, interfaces, and specialized electrical isolation are designed for and can be used for the implementation of the MGHAE.
Many times patients make doctor's appointments, travel to the physician's office, and possibly exposed themselves to diseases, only to find out that their biological parameter profiles are normal. An exemplary embodiment of the present disclosure includes the disclosure of a medical grade data portal to access a medical grade module connected to standard electronic and displays of Household Appliances and Household Electronics (HAHE), wherein medical parameters are able to be logged and displayed. Unnecessary travel to a hospital or doctor's office and exposure to others could be minimized, and the onset of possible disease conditions could be caught before developing complications. Preventive medicine in the very best sense would become a reality since people who need to buy a HAHE, for example a television, will at the same buy a medical device for monitoring biological parameters without the cost, complexity, and large size that characterizes standard medical devices of the prior art.
Telephone or internet connections would provide a path by which the biological parameters measured could be transferred to a health care professional qualified to read and analyze the biological parameters. The special medical grade interface of the present disclosure includes, by way of illustration, in a television-set, allows said television-set at home to display and store the value of any biological parameter and to display, for example, a temperature profile of a person having a bout of influenza. This disease pattern caused by the influenza can be overlaid on the subject's baseline temperature. This baseline temperature, with the features described in the present disclosure, can be acquired effortlessly when the user is watching a television program. A person can be watching a television program while a heart rate waveform, electrocardiogram waveform, or a temperature level is simultaneously displayed (and recorded) in a similar manner as stock ticker symbols and numbers or news headlines displayed on the bottom portion of a television screen by an A/D converter broadcasting network. The difference is that the number for the stock displayed is generated by the television network, while in the present disclosure, the biological parameter number displayed is generated by the television electronic circuitry itself based on the data received from the medical monitoring device through the Medical Grade Module (MGM). Moreover, the interface module is able to display digital numbers representing the level of concern. Appropriate instructions are displayed and the phone number(s) that might be desired for further information are displayed, such as drug names, pharmacy names and locations, doctor's names, laboratories, hospitals, and any other information relevant to the biological signal being received. The signal from MGHAE 8414 can be conveyed to numerous providers and locations that are related to the information being received from medical monitoring device 8416, so if high blood pressure is identified during monitoring, a doctor can be contacted and the information on blood pressure is automatically transmitted.
It is understood that any household appliance or household electronic device are within the scope of the present disclosure. By way of illustration, but not of limitation, a stove having a display and the medical grade port and medical grade module of the present disclosure provides monitoring of biological parameters while a subject is cooking or waiting for food to cook. In this exemplary illustration, the medical grade port is connected to a blood pressure measuring system adapted to work in connection with the medical grade port, which is used to monitor the subject's blood pressure continuously while waiting the food to cook.
Creation of specific systems and sub-systems as described in the present disclosure enables common household appliances and electronics to be turned into medical grade monitoring devices. The range of appliances may include, but is not limited to, a television, camera, stove, washing machine, dryer, refrigerator, microwave oven, computer, cell phone, watch, eyeglasses, music player, video game, telephone, electronic thermometer, and any other device having the electronics, reporting, and input means required for the functions described herein. Any device that has a reporting system, preferably a visual and audio system, is within the scope and can be enabled for medical monitoring. Moreover, the ability of household appliances and electronics manufacturers to offer a medical grade diagnostic to customers will create a new generation of household appliances and electronics with diagnostic and therapeutic capabilities.
The inventions of the present disclosure have several advantages. First, the inventions of the present disclosure will preferably harness power that is present in a variety of household appliance and electronic devices, including but not limited to: computers, television, refrigerators, microwave ovens, radios, thermostats, air conditioners, clocks, cell phones, or telephones. Second, the inventions of the present disclosure are typically low cost and easily adaptable into a variety of household devices. Third, the inventions of the present disclosure include communication between medical monitoring or measuring devices and household devices with a microcontroller or processor circuitry. Fourth, the inventions of the present disclosure use universal medical cables available in the medical industry to allow a variety of biologic monitoring devices to be coupled to household electronics and appliances.
In addition to medical systems communicating by wire, MGHAE 8414 includes communication via wireless transmission as well. In this alternative exemplary embodiment, the household and electronics appliances include a wireless transmitter or transceiver.
In another exemplary embodiment of the system, MGHAE 8414 includes a payment system in which the manufacturers of household appliances or electronics will have the ability to charge the user a fee for use of the monitoring system.
The inventions of the current disclosure allows users to bring a device, such as a cell phone that received the information captured by MGHAE 8414 to their medical professional to have their vital signs reviewed. Alternatively, connection of MGHAE 8414 to the internet or via a cellular network allows a patient to transmit vital signs or other measured information through a network or the internet. The stream of information has a stamp with the original signal with the identification of the household appliance or electronics sending the information.
A benefit of the inventions of the current disclosure is to have the ability to have full medical monitoring in the comfort of your home. Such monitoring saves money on gas, insurance, time, and the environment. This monitoring will also allow for decreased absenteeism at work and increased productivity. By way of illustration, medical grade computers, allows medical monitoring at work (while working on a desk). Thus, the work environment will provide the ability to monitor vital signs continuously while people are at work. By way of another illustration, medical grade television sets allow medical monitoring at home, for example, while watching television. Thus, the home environment provides the ability to monitor vital signs continuously while people are at home. By way of yet another illustration, example, or embodiment, medical grade video game sets allow medical monitoring at home while playing video games. Thus, the entertainment environment will provide the ability to monitor vital signs continuously while people play. By way of yet another illustration, example, or embodiment, medical grade washing machines allow medical monitoring at home while doing household chores. Life expectancy can be increased be improved, cost-effective monitoring. Physical fitness can also be monitored by using MGM 8422 in exercise machines according to the various principles of this disclosure.
MGHAE 8414 of the current disclosure also includes electronics and software to enable monitoring and treating of various diseases. In addition, MGHAE 8414 can include an alarm for values or wave forms that fall outside a pattern of normality (ex: EKG, heart rate, oximetry, oxygen, blood gas, blood pressure, eye pressure, etc.).
By including a second port on the medical grade appliance (TV, Internet connected data logger, etc.), various device manufacturers will have an opportunity to communicate with the host. As used herein, host is a device that receives and processes signal received from medical sensors. The host device is configured so that the manufacturer is able to communicate with the device, while biological information is captured and stored in the host device, for example, a television, in a separate location that is inaccessible to the manufacturer. The primary port that would normally be used by the appliance manufacturer for service, diagnostics, etc., would remain in a default mode dedicated to the manufacturer's communication protocols and use. When the second port is connected to a medical device (temperature, heart rate, blood pressure, etc.), that device uploads to the appliance its ID and how it intends to communicate with the appliance's main port. Alternatively, the medical grade port communicates with the main port, or yet the main port is combined with the medical grade port into one single port.
Inventions of the present disclosure allow medical devices from different manufacturers to communicate and use the display, recording abilities, alarm modes, etc., of the host household appliance, such as, by way of illustration or example, a refrigerator, washing machine, video game or television, without the worry of altering, disrupting, or interfering with the operation of the host household appliance. To preserve the household function intact, such as television settings, stove settings, camera settings, computer settings, and the like, only certain commands or types of data necessary to effect permitted actions are allowed, thereby protecting the internal settings and programmed functions of the host, namely the HAHE, which may be, by way of illustration, a television. It should be understood that those new MGHAE can be constructed as a separate physical device, such as the interface module disclosed herein for monitoring temperature with ABTT Monitoring System 8000, or, alternatively, the medical grade module and system can be integrated into household appliances. In this exemplary embodiment, the appliance manufacturer only allows certain commands or types of data necessary to effect permitted actions (protecting the internal settings and programmed functions of the host). MGHAE 8414 of the present disclosure includes a medical monitoring device and a control system in the host household appliance, with said control system preferably controlling the medical monitoring device.
An exemplary embodiment with a second port allows creation of security and a degree of standardization between various types of input devices. A “hub” allows several different instruments to be connected at the same time, sharing the appliance on a time basis.
As an example, the user may wish to do a thermal scan and send it to his/her doctor. If the appliance is a TV, when the scan is performed, the current “program” is minimized, the temperature scan is displayed and sent to the doctor's office for analysis.
Any medical device, or any device measuring a biologic parameter can be used. By way of illustration, but not of limitation, the present disclosure includes a thermographic device for thermal mapping of the ABTT for identifying an abnormal condition in the body, or by using a thermal sensor as disclosed herein. In the example of a computerized infrared scanner, if the image detects an abnormal condition, that information on abnormal condition is displayed or reported by visual or audio means in the MGHAE, using the display and speakers that are already part of the regular household appliance, but now are transformed into a medical alert reporting system. In the example that uses continuous thermal sensing, the acquired curves are compared to curves that were stored in the memory of household appliances. These acquired curves, for instance when the subject is watching television, can be compared to the subject's baseline pattern, or compared to predetermined patterns that indicator disease or an abnormal condition, or a change in physiological condition, such as ovulation. The standard controller or processor in the MGHAE is adapted to identify an abnormal pattern and alert the user or subject. With the present disclosure, a television, such as a smart TV for example, is adapted to become medical grade for coupling with the medical grade module of the present disclosure and a subject can thereby see and record the biological data being capture. By way of illustration or example, even a digital photo camera that includes electronics and memory can receive biological signals and operate in a similar manner as described for standard household appliances. Although the illustration hereinabove used a temperature sensor and temperature profile stored in the non-transitory memory of the MGHAE, it should be understood that any device measuring a biological signal can be used, such as measuring blood pressure, heart rate, oxygen and oximetry, glucose, and the like, and any device measuring any medical parameter such as EKG (electrocardiogram), electroencephalogram (EEG), and the like.
This portion of the present disclosure includes disclosure of a medical grade household electronic and appliances for monitoring biologic parameters using a medical grade module and a medical grade port, including continuous display of the data being monitored in the household appliance. However, it should be understood that a single measurement or intermittent measurements of biological signals are within the scope of this inventions. By way of illustration, if an altered glucose level (or fever) is identified, that single number can be reported by the MGHAE, using the same processing means, reported means, and stored values. In this embodiment, for example, the stored value in the memory of the MGHAE would be an abnormal glucose level. Hence, by way of illustration, if a level of glucose higher than 150 mg/dl is identified, that higher level is reported by visual and audio means of the MGHAE.
It should be understood that any medical measuring device can be continuously operatively coupled to the MGHAE. In accordance with other embodiments of the present disclosure, in which standard medical devices (including blood pressure measuring device, thermometers, blood glucose measuring devices and the like) are operatively coupled by wired or wireless means to standard household appliances (such as television, computer, cell phones, watches, eyeglasses, refrigerators, microwave ovens, stoves, washing machine, air conditioner, and any household appliance that has any reporting apparatus, including audio or visual). By way of illustration, the subject measures his/her blood pressure (or glucose level), but the subject is not watching television during the measurement and is away from the television. The data collected during the measurement is transmitted to all enabled household appliances. Once the subject turns the television on, for example, the collected data is displayed. If the measurement identified abnormal levels, the medical grade module turns on the television to display the abnormal value. Likewise, the display of a microwave oven, instead of displaying the time or cook settings, uses the LED or a numerical display to display the abnormal value. In the vast majority of cases, complications in patients occur due to lack of compliance with taking medications, and inventions in accordance with the teachings of this disclosure provide a system and device to inform and warn the user about the abnormal levels. Further, the devices and systems of the present disclosure prompt or urge the user or patient to take medications for correcting such abnormal levels; for example, taking a blood pressure medication, antibiotic, or insulin. It should be understood that standard appliances can also display the medication to be taken, said medication information being stored in non-transitory memory of the standard household appliance. It is also understood that the MGHAE can also display the medication to be taken, said medication information being stored in the non-transitory memory of the MGHAE.
Medical monitoring device 8416 includes, but it is not limited to, measurement of any biological parameter such as blood pressure, eye pressure, heart rate, temperature, oxygen, blood gas, chemical compounds, drugs, analytes, glucose, oxygen saturation (oximetry), blood components, and device for sensing, detecting, or measuring any biological parameter including physical parameters and chemical parameters. Medical monitoring device 8416 provides an output preferably after MGHAE 8414 provides power for medical monitoring device 8416. The setting of medical monitoring device 8416 is then done according to a computer program installed in MGHAE 8414, with a user interface that utilizes a display (not shown) of the host for displaying a control panel for medical monitoring device 8416. Using controls located in MGHAE 8414, medical monitoring device 8416 is activated. MGM 8422 of MGHAE 8414 has processing circuitry adapted to control medical monitoring device 8416, and operation of medical monitoring device 8416 is made from the processing area of MGM 8422. For example, when using a medical grade television 8428, shown in
In another embodiment, the remote control (not shown) of television 8428 functions as the control panel for medical monitoring device 8416. The biological data is then displayed on the display of the host device, referred herein as host display, i.e., the display of MGHAE 8418, which is, for example, the display screen 8438 of television set 8428 in the exemplary embodiment of
In an exemplary embodiment, medical grade port 8424 is a bi-directional multi-pin port that allows analog as well as digital information to pass between the medical device (e.g., medical monitoring device 8416) and the appliance's internal module adapted to be coupled to a medical monitoring device. It should be understood that MGHAE 8414 can be adapted for connections with standard medical devices produced by a variety of medical device manufacturers. All pins of medical grade port 8424 of MGHAE 8414 are electrically isolated, providing ground and shock protection to users, following ISO 60601 and UL standards. By allocating a certain number of input pins of medical grade port 8424 for analog measurements, some medical instruments (e.g., medical monitoring device 8416), through the present disclosure, can be made available at a lower cost by not requiring a power supply or amplification. In an exemplary embodiment, the host portion of MGHAE 8414, which may also be described as the appliance portion, includes an internal A-to-D converter, such as A/D converter 8436, which has a programmable gain “front end” and allows various analog sensors to be directly monitored. Some of the pins output a variable voltage to control or program the medical instrument (e.g., medical monitoring device 8416), represented as a digital to analog conversion provided by a D/A converter 8437 included as part of MGHAE 8414.
Medical grade port 8424 in accordance with an exemplary embodiment of the present disclosure supports standard RS-232c serial (0-5 volt) communications as well as USB and several industrial protocols. Digital pins in the connector are programmable as inputs or outputs, depending on the device (medical monitoring device 8416) connected. Some of the pins of medical grade port 8424 provide power to the external device (3.3 volts, 5 volts, etc.) eliminating the need for batteries and their disposal.
An example of an instrument that could take advantage of the analog aspect of medical grade port 8424 of this disclosure is Abreu BTT temperature sensor or probe 8442 (wearable continuous sensor or quick read contact “pen”), as shown in
There are an increasing number of “smart sensors” that operate at very low power (voltage and current) that perform signal processing internally and that transmit data digitally, when requested, over just one signal line. An example of one such sensor is an infrared temperature sensor that enables non-contact skin temperature measurements and graphing. Two such sensors on a wand (side by side), in accordance to the principle of this disclosure, provide a very inexpensive tool for scanning.
In another embodiment, inexpensive integrated circuit pressure transducers, such as the pressure transducers manufactured by Motorola, directly connect to the analog pins in medical port 8424 of the present disclosure, enabling inexpensive pressure and force gauges to be part of the home medical “tool” box (grip strength, scales, lung vital capacity, FEV (forced expiratory volume), etc.).
In another embodiment, the information collected through medical port 8424 from these various instruments is formatted within host electronics 8426 of the appliance and re-transmitted (encrypted) through the appliance's USB port to a computer for further analysis, storage, display, or transmission over the internet as an encrypted data file. However, it should be understood that in some embodiments of the present disclosure that MGHAE 8414 includes in its MGM 8422 a processor and memory adapted for analyzing and storing medical data received via medical grade port 8424, and for communicating said medical data for displaying on a display of MGHAE 8414, such as for example display screen 8438 of television set 8428.
In addition, in another exemplary embodiment, the data/pictures stored in MGM 8422 are transferred from MGM 8422 into a conventional memory stick or flash card (not shown), which can then be brought with the patient to the doctor's office or hospital.
In another embodiment, a medical enabled bedside clock radio is connected to medical monitoring device 8416, for example a continuous measuring Abreu BTT temperature probe in any of the exemplary embodiments described herein, and cause the alarm/radio to turn on when certain “fever” or “chill” set points are exceeded. The same temperature information is transmitted to a clock in the parents' room, which can be enabled to display their child's temperature. In this exemplary embodiment, the clock radio includes a wireless transmitter coupled to a second clock radio. It is understood that any device having a clock and alarm, such as a cell phone, is within the scope of the disclosure. In the embodiment in which MGHAE 8414 is represented by a cell phone, the cellphone includes MGM 8422 and medical grade port 8424, with said cell phone being connected to medical monitoring device 8416 and using its alarm function to activate the warning based on a certain predetermined level of the parameter measured, for example, a certain level of blood pressure, glucose, heart rate, insulin, drug levels, oxygen, oximetry, respiratory rate, and the like.
The ability to utilize programmable, internal, computerized circuitry within an appliance that would normally be in the home for medical monitoring purposes has tremendous impact on all aspects of home care for the elderly, for individuals with medical conditions that would otherwise require continuous monitoring, and in other situations when continuous medical monitoring is desirable but not possible. Almost every nursing home supplies a television in each patient's room, with each television connected by cable to a central point. If each television were medically enabled, as described in the present disclosure, every patient room would have instant patient monitoring capability with no additional wiring required in the facility. In addition, MGHAE 8414 already occupies space to perform an appliance function, such as television, computing, etc., and transforming an appliance requires no additional space on a shelf, on the floor, or on a wall to provide its medical monitoring function.
Software can be easily installed in MGHAE 8414 via medical grade port 8424, to guide the operation of MGM 8422 and to transmit the input received from medical monitoring device 8416 to, for example, processor or controller 8432 and display 8438 for analysis and/or display of data.
In another exemplary embodiment, as seen in
The household appliances and household electronics, in accordance to the present disclosure, are configured for a single or multiple data input from a single or multiple MMD's, which are directly connected to MGM 8422 of the HAHE via a medical grade port, thereby allowing the HAHE to store, analyze, and display the biological data. The present disclosure thereby provides a MGHAE, for example a television set, that processes, stores, and displays various types of biological data using one single MGHAE, for example a television set.
In an exemplary embodiment for measuring temperature using the Abreu ABTT system, shown in
In another exemplary embodiment, shown in
Moreover, since medical grade module 8476 includes controller 8480, A/D converter 8482, and non-transitory memory 8482, all of those components which are currently present in a variety of biological monitoring devices and measurement systems are eliminated from said devices and systems, thereby reducing cost of the medical devices since one HAHE can be used to monitor a series of medical monitoring devices, and there is no need for additional screens, processors, memory, converters, and the like. The present disclosure provides the most cost-effective medical device since the medical device only include a sensor, a wire, and a connector to connect to the medical grade port, and/or a wireless transmitter.
In an exemplary embodiment, the primary port that would normally be used by the appliance manufacturer for service, diagnostics, etc., would remain in a default mode dedicated to the manufacturer's communication protocols and use. When a second, medical grade, port is connected to a medical device that measures temperature, heart rate, blood pressure, etc., the medical device loads its ID to the appliance and how it intends to communicate with the appliance's main port.
Generally, the output signal of most temperature sensors is analog. However, some temperature sensors include an integral A/D conversion, and the output may be input directly into a controller without conversion, providing a highly accurate measurement signal and eliminating the need for an A/D converter. However, this input needs to be on connector pins that connect directly to the controller rather than pins normally used for A/D conversion to reduce the chance that the signal is erroneously read if the temperature sensor or other medical monitoring device with a digital output is attached to a device with an A/D converter.
Digital data lines 8516 going to medical grade port 8506, which are usually in groups of 8 or 16 lines, are programmable as inputs or outputs as the situation may require for MGHAE 8498 acting as a diagnostic (input) or therapeutic (output) device.
In another exemplary embodiment, 8514 also controls a digital to analog (D/A) converter 8518 providing programmable voltage levels to an external medical device, allowing control of some sensors or therapy equipment without the need for additional circuitry within the connected sensor, therapy equipment, or other medical device.
A communication section or unit 8520 has the necessary components and wires to communicate directly with “smart” devices containing microprocessors using standard serial, USB, RS-232, or other protocols. An RF link, unit, or module 8522 includes hardware for wireless communication to a device or a series of devices in close proximity, with close proximity being at least feet, but could be tens of feet. Several different standards exist for intelligent “polling” and control of multiple RF linked transceivers that all interact with each other and can “pass” information packets from one to another to reach all those involved in a necessary task; i.e., the linked RF transceivers form an ad hoc local network. The present disclosure uses a saltatory transmission, in a similar manner as nerves impulses hop along axons. As shown in
Medical grade module 8500, which may be positioned in a television or MGHAE 8534 in a patient's room, displays the temperature on television 8534 or a clock radio 8536, and turns on a wirelessly connected alert light 8538 outside a patient's or subject's door, which sends it “down the line” to a nurse's station 8540. In an exemplary embodiment, a network of appliances and electronics is disclosed: Smart appliances, which include a medical grade module such as medical grade module 8500, the medical grade module further including wireless transmitters, circuitry, and controllers programmed for sequential transmission of a signal, when receiving a signal from a medical device with said signal falling outside a pattern or level of normality, or falling outside a predetermined level for the signal, activates transmission of that signal to the nearest appliance, and to a subsequent appliance until arriving at a central station (e.g., nurse station). These “smart medical grade modules” can be used in any environment and require little power because of their short transmission range.
When medical grade module 8500 is “awakened” by receiving an abnormal signal, medical grade module 8500 transmits that it was “awakened” to all adjacent medical grade modules and appliances containing the proper handshake protocol or encryption enabled communication over a discrete area, such as an entire house, floor of a hospital, wing of a hospital, etc., until finally reaching a central receiving medical grade module 8542, which may be a personal computer, laptop, tablet, or similar device, a server, a desktop computer, or a mainframe, where the identification of MGHAE 8498 that was “awakened” far away from central medical grade module 8452 is decoded and recorded. Furthermore, central medical grade module 8452 may communicate via one or more routes, including internet, cellular networks, Wi-Fi, and landline, to one or medical professionals that a condition exists which may require attention or correction, and in some cases, an emergency condition that requires immediate attention. In practice, medical grade modules may be communicating with medical grade modules that are inches apart to many feet apart.
An illustration will clarify the advantages and innovation of the present disclosure related to the saltatory transmission: a household has a plurality of appliances and electronics disposed in its various areas, inside and outside the house. Those appliances remain unused most of the time. However, these appliances and electronics have a variety of host electronics, transceivers, displays, etc., and the inventions of the present disclosure uses said host electronics, transceivers, display, etc. for reporting or communicating signals (preferably abnormal signals) to each other. For example, a house may have three rooms located in different parts of the house, each of said rooms having a child in it and each child has a medical device monitoring biological parameters. By way of example, one child (with heart problems) has a heart rate monitor, one child (with an infection) has a temperature monitoring device, and one child (with asthma) has an oxygen (or oximetry) monitoring device. The parents are outside working in the back yard away from her children. Once the child with an infection starts to develop fever, the signal is recognized by a processor integral to the medical monitoring device, based on comparison of the received signal with predetermined values for normality stored in non-transitory memory, as abnormal. The processor is programmed to recognize the abnormal signal and then to activate a wireless transmitter (in an exemplary embodiment, the transmitter is short range one, but any transmitter can be used—an exemplary transmitter includes a Bluetooth), to transmit the signal to the nearest appliance enabled with a smart medical grade module, such as medical grade module 8500. In an exemplary embodiment, the wireless transmitter is integral to the medical monitoring device, but it may be a separate wireless transmitter.
For example, the child with fever is in room with a medical grade television, which receives a signal from a medical monitoring devices that “awakens” the television with the abnormal signal. Once medical grade module 8500 in the television is awake, controller 8514 transmits a signal via RF link and, if available, communication section 8520 to all medical enabled appliances in range. For example, the television transmits its signal to the next room and “awakens” a video game including a medical grade module, which may also be similar to medical grade module 8500. Once the medical grade module of the video game is “awake,” the medical grade module of the video game transmits the signal to an electronic clock in the living room that includes a medical grade module. The medical grade module of the electronic clock in the living room then awakens an enabled microwave in the kitchen. The medical grade module in the microwave then awakens the medical grade module in a central station presently position outside in the back yard, which then flashes a red light, or reports the information via a display. Once the abnormal signal reaches the central station outside, the ID (identification) of the medical monitoring device that was disturbed far away is provided to the central station outside, thereby identifying the child generating the abnormal signal. In an exemplary embodiment, the reporting apparatus includes a red light for the child with fever. If the child with asthma was sending the abnormal signal, then the light activated would be blue, and if the child with heart problems was transmitting the signal, the light activated would be yellow. This differentiation of signals allows the parents to know immediately and precisely which child requires assistance. At night, the central station can be in the parents' room, so if any child during the night has a problem the abnormal signal would be transmitted to the parents' room using all medical grade module enabled appliances and electronics.
Although the present embodiment was described for medical care in a house, the system can have a plurality of applications. For example, a burglary alarm, in which opening a door or window at a certain time of the night awakens other medical grade module enabled appliances that will transmit signals to the central station, possibly indicating a burglary in progress. The same apparatus configuration can apply to an alarm system in a bank, or alarm system in a hospital, and the like. The present embodiment takes advantage of the low price of wireless transmitters (e.g. Bluetooth) and of electrical and electronic appliances already in use to create a precise, efficient, and low cost alarm system. Any electrical devices outside the house can be enabled with a medical grade module and used as part of the sequential alarm system of the invention, including a chain saw, lawn mower, leaf blower, snow blower, weed trimmer, electrical pump, or any other device that either has a battery or is connected to an electrical outlet, so as to power the medical grade module in an embodiment in which the medical grade module does not have its own power supply. Preferably, electrical power is derived from the standard (and already used) connection of the appliance or electrical device to an electric outlet.
Magnetic or optical isolation 8544 would transfer the necessary digital data between medical grade module 8500 and host appliance 8502. Isolation 8544 is a two-way path covering control signals and data to medical grade module 8500 or to/from a medical monitoring device directly.
The MGHAE, also referred herein as Medically-enabled household appliances and electronics (MEHE) include an embodiment, shown in
Applicant has recognized that patients are often diligent about taking certain actions when specifically reminded. For instance, patients will bring their blood pressure measuring device to a doctor's appointment when reminded by someone in the medical professional's office. In many instances, patients measure their blood pressure (BP) and read levels that are high and in some instances alarming. In one exemplary example, a patient X had spent the weekend prior to having a stroke watching television, listening to music, cooking, and working on a computer. Despite high BP levels measured that same weekend, patient X did not take medications for lowering blood pressure, nor did patient X contact a doctor. It appears that patient X was focused on media, information devices, and even cooking, such that patient X “forgot” to address a high BP problem. Unfortunately, patient X suffered a stroke and became permanently disabled. Even more unfortunately, patient X's situation appears to be somewhat common in individuals with potentially life-threatening conditions. Applicant further recognized that this situation appeared even more common among individuals who lived alone.
Applicant recognized that a uniquely enabled system, such as that shown in
The capability to measure the temperature of the skin over the ABTT terminus and to analyze that information provides new capabilities for safety in the operation of equipment. Referring to
In an exemplary embodiment, vehicle 8550 includes a vehicle system controller 8552, which is connected to a braking system 8554, a lighting system 8556, and a vehicle control system 8558. Vehicle 8550 may also include a near-field communication system 8560, a speaker system 8562, an external communication system 8564, and a sensor system 8566.
Vehicle system controller 8552 is connected to a non-transitory memory 8553, which provides information and routines to vehicle system controller 8552.
In an exemplary embodiment, lighting system 8556 includes a lighting system controller 8568, which is connected to a plurality of vehicle lights 8570. As discussed further herein, one or more systems in vehicle 8550 may command lights 8570 to operate. For example, switches may directly command headlights, and turn signals. Actuation of brakes may command brake lights. The request for lights may go directly to lighting system controller 8568, or may go to vehicle controller 8552, which sends control signals to lighting system controller 8568.
In an exemplary embodiment, braking system 8554 includes a braking system controller 8572, which is connected to vehicle system controller 8552 and a plurality of individual brakes 8574. Braking system controller 8572 controls the amount of braking provided by each one of the plurality of individual brakes 8574, each of which is positioned close to one of vehicle 8550 wheels (not shown). Braking commands by an operator may be routed to vehicle system controller 8552, which then routes the braking command to braking system controller 8572, or, in another exemplary embodiment, braking commands are directed from a brake pedal or other brake actuator (not shown) directly to brake controller 8572.
In an exemplary embodiment, vehicle control system 8558 includes the controls the operator uses to operate the vehicle. Operator controls are typically positioned on or near a dashboard 8576. Controls included in control system 8558 may include an override switch 8578, a display 8580, a steering column and wheel 8582, and a steering control unit 8584. Steering control unit 8584 may be commanded by movement of steering column and wheel 8582, or it may be controlled by vehicle system controller 8552, as described further herein. Display 8580 provides operator alerts on dashboard 8576. Other types of operator controls exist. However, such controls are not discussed in this disclosure.
In an exemplary embodiment, near field communication system 8560 may include one or more system elements, such as a near field transceiver 8586, which is connected to and communicates with vehicle system controller 8552. Near field communication system 8560 may be, for example, a Bluetooth connection.
In an exemplary embodiment, speaker system 8562 may include an amplifier 8588, which may be connected to vehicle system controller 8552, and at least one speaker 8590, which is connected to amplifier 8588. Sound signals may be directed into vehicle system controller 8552, which then directs the sounds signals to amplifier 8588, or vehicle system controller 8552 may generate sound signals, which are provided to amplifier 8588 and, ultimately, speaker 8590.
In an exemplary embodiment, external communication system 8564 includes a transceiver 8592 and an antenna 8594. External communication system 8564 may be a system that communicates with a remote location for emergency communication, roadside assistance, etc.
An operator 8596 of vehicle 8550 has an ABTT temperature sensor 8598 positioned to measure the temperature of the skin over the ABTT terminus 8600. ABTT temperature sensor 8598 is connected to a battery and a near field transceiver or transmitter 8602. The battery to power ABTT temperature sensor 8598 and the transceiver that connects ABTT temperature sensor 8598 to near field communication system 8560 may be located in many different places, such as a hat 8604, eyeglass frame (not shown), headband (not shown), or other locations.
A safety function of vehicle 8550 is described with respect to
In NFC process 8614, NFC system 8560 is powered, and NFC system 8560 determines the presence of operating NFC devices that have been properly connected to NFC system 8560. One such NFC device is transceiver or transmitter 8602, which is connected to ABTT temperature sensor 8598, which is positioned to measure the temperature of the skin over ABTT terminus 8600. If transceiver 8602 is operating, NFC system 8560 will initiate communications with transceiver 8602. Once communication is established with transceiver 8602, control passes from NFC process 8614 to a power temperature sensor process 8616.
ABTT temperature sensor 8598 may be powered by a switch located on ABTT temperature sensor 8598, or on battery and transceiver 8602, or elsewhere. In an exemplary embodiment, transceiver 8602 may contain electronics to automatically power ABTT temperature sensor 8598 once communication with a controller enabled to receive temperature data has been established. In an exemplary embodiment, ABTT temperature sensor 8598 is powered only while receiving temperature data, and remains off at other times. In another exemplary embodiment, ABTT temperature sensor 8598 may be powered by a battery pack located in hat 8604. In yet another exemplary embodiment, ABTT temperature sensor 8598 may be powered by vehicle 8550, which may be accomplished by a connection to a power outlet of vehicle 8550 or through other apparatus. Once power has been provided to ABTT temperature sensor 8598, control passes from power temperature sensor process 8616 to a transmit data process 8618.
In transmit data process 8618, ABTT temperature sensor 8598 reads temperature, which is presumably the temperature of ABTT terminus 8600, and sends a signal representing the temperature data to transceiver or transmitter 8602. The data from ABTT temperature sensor 8598 is analog. This analog data may be converted to digital data by an A/D converter located in proximity to or contained as a part of transceiver 8602. Alternatively, the analog temperature signal may be provided to transceiver 8602 for transmission. Transceiver 8602 transmits the temperature data to vehicle near field transceiver 8586. Near field transceiver 8586 transmits a signal to vehicle system controller 8552 that represents the temperature measured by ABTT temperature sensor 8598. Control then passes from transmit data process 8618 to a data analysis process 8620.
In an exemplary embodiment, data analysis process 8620 is performed in vehicle system controller 8552. However, data analysis process 8620 may be performed in a controller (not shown) specifically configured to process temperature data. In another exemplary embodiment, temperature data may be transmitted to a portable controller (not shown) specifically configured to process temperature data, and data transmission is from the portable controller to vehicle system controller 8552.
Data analysis process 8620 performs several functions. First, data analysis process performs a validity check on the temperature data. This validity check determines whether the temperature data is measuring the temperature of ABTT terminus 8600. If the temperature data is not valid, in an exemplary embodiment, vehicle system controller 8552 provides a visual alert to operator 8596 via vehicle display 8580, an audible alert to operator 8596 via speaker 8590, or other types of alerts that may include seat vibrations, steering wheel shakers, cell phone ringing alerts, etc. Failure to properly measure temperature may be because ABTT temperature sensor 8598 is not operating properly, because it is misaligned with ABTT terminus 8600, because it is malfunctioning, because insufficient power, improper communications, or for other reasons. If the temperature is not valid, it will be considered a not normal condition for other safety system 8610 processes.
If the temperature data is valid, data analysis process 8620 analyzes the temperature data for at least one condition of operator 8596. Once such condition may be a drowsiness or sleepiness condition, such as that described in connection with
In normal temperature data decision process 8622, a process path is chosen based on whether temperature data is valid and normal or whether the temperature data is not normal. A not normal condition may be indicated because the temperature data is invalid or because the temperature data indicates an operator 8596 impaired condition. If the temperature data is valid and normal, control passes from normal temperature data decision process 8622 to continue operating vehicle decision process 8624.
In continue operating vehicle decision process 8624, safety system process determines whether operation of vehicle 8550 is continuing. Such decision may be made on the basis of continued operation of various vehicles systems, such as a combustion system (not shown), an ignition key (not shown) position, or other indicators of continued vehicle operation. If operation of vehicle 8550 is continuing, control passes from continue operating vehicle decision process 8624 to transmit data process, and safety system process 8610 continues as previously described herein. If operation of vehicle 8550 is ceasing, control passes from continue operating vehicle decision process 8624 to a remove power process 8626.
In remove power process 8626, power to ABTT temperature sensor 8598 is removed, power to transceiver or transmitter 8602 is removed, and various vehicle systems are powered down as operation of vehicle 8550 ends. During this process, certain data, potentially including temperature data from ABTT temperature sensor 8598, may be stored in non-transitory memory 8568 to be used the next time vehicle 8550 is operated. It should be apparent that multiple operators may use vehicle 8550, and each ABTT temperature sensor 8598 may be associated with a specific individual, or an individual ABTT temperature sensor 8598 may be associated with a specific operator via a vehicle input (not shown). Thus, temperature data may be stored in non-transitory memory to establish a baseline for current measurements. Once power has been removed from vehicle systems that are associated with operation of vehicle 8550, control passes from remove power process 8626 to an end process 8628, which ends safety system process 8610.
Returning to normal temperature data decision process 8622, if the temperature data is not valid or normal, control passes to an initiate operator warnings process 8630. In initiate operator warnings 8630, in an exemplary embodiment, display 8580 may provide an indicator or warning that temperature data is not valid, indicates an impending impairment condition, such as sleep or a medical condition, or indicates that an impairment condition is occurring. In another exemplary embodiment, an audible warning may be provided by speaker system 8562. Such audible warnings may be tones, warbles, alarms, etc., or may be an audible warning, for example: “Temperature data invalid,” “Impairment condition imminent,” or “Driver Impaired.” Once one or more operator warnings have been initiated, control passes from normal temperature data decision process 8622 to an operator override decision process 8632.
In operator override decision process 8632, operator 8596 has an opportunity to override any further action by safety system process 8610 by providing an input to vehicle system controller 8552. In an exemplary embodiment, such input may be by way of a switch, such as override switch 8578. In other exemplary embodiments, inputs may be via a touch screen on a display, such as display 8580, via voice command, via gesture, or other via other apparatus that reduces or prevents inadvertent override commands. Reducing the chance of inadvertent override commands may including placing override switch 8578 behind a protective shield that is required to be lifted, by biasing override switch 8578 into an off position, requiring the bias to be moved to actuate override switch 8578. For purposes of continued operation and in an exemplary embodiment, operator override decision process 8632 may automatically consider an invalid temperature data condition as an automatic operator override. If operator 8596 selects override, or if temperature data is invalid, control passes from operator override decision process 8632 to transmit data process 8618, and operation of safety system process 8610 continues as previously described.
If operator 8596 does not indicate or select override of initiated warnings, and if temperature data indicates an impending impairment condition or active impairment condition, control passes from operator override decision process 8632 to an initiate vehicle warnings process 8634. The function of initiate vehicle warnings process 8634 is to warn drivers around vehicle 8550 that the operator of vehicle 8550 is suffering from an impairment condition, which may be sleep, medical, or other impairment condition that may be detected by ABTT temperature sensor 8598. In exemplary embodiments, such warnings may be flashing of one or more external lights 8570, including flashing in specific patterns, flashing of special “impairment” lights 8570 located in non-traditional locations, such as the sides of vehicle 8550, along the doors of vehicle 8550, or in other locations. In an exemplary embodiment, vehicle lights 8570 may include a new type of lighting for vehicles comprising a medical alert light, which, when activated, indicates medical emergency and risk of accident by the driver being incapacitated. These lights may include a new set of lights in vehicles, such as two rear lights and two front lights that flash only in medical emergencies. In another exemplary embodiment, conventional vehicle lights 8570 could be activated in a strobe (high frequency) level to alert other drivers and people. In yet another exemplary embodiment, a sign 8571 indicating “impaired,” “medical,” or other word or symbol, such as a red cross or caduceus may be present in a location visible at least from one of a back, front, or side of vehicle 8550. In another exemplary embodiment, impaired or medical light 8571 may be present on the top of vehicle 8550, providing for rapid identification of vehicle 8550 from the air by helicopters or airplanes responding to an emergency request. In another exemplary embodiment, warnings may be audible external to vehicle 8550, such as sounding of a car horn or speakers warning of an impaired operator. Such audible warnings may be a specific pattern of tones or sounds that may be adopted to indicate impaired operator. External vehicle warnings will continue at least until vehicle 8550 is turned off, though such warnings may require a reset specifically to stop external vehicle warnings, such as by actuating override switch 8578. Once vehicle warning(s) have been initiated, control passes from initiate vehicle warnings process 8634 to a control vehicle process 8636.
In control vehicle process 8636, controller 8552 takes control of vehicle 8550 to the extent that controller 8552 is enabled to bring vehicle 8550 to a controlled stop in the safest manner possible. In an exemplary embodiment, such control may be actuating braking system 8572 to activate individual brakes 8574. In an exemplary embodiment, such braking is configured to be a rapid stop, but not an emergency stop where brakes are locked up and tires screech, because such a stop risks a rear end collision in the presence of another vehicle behind vehicle 8550. In another exemplary embodiment, controller 8552 may be enabled to control steering wheel 8582 via steering control unit 8584, such that controller 8552, by receiving inputs from sensor system 8566, is able to steer vehicle 8550 onto a shoulder or side of a road out of traffic, and then provide braking to vehicle 8550. Once control vehicle process 8636 is complete control passes to a call for help process 8638.
In call for help process 8638, if vehicle 8550 is configured with an external communication system 8564, vehicle system controller 8552 will initiate a call for help via antenna 8594. Alternatively, vehicle 8550 may be coupled to a cell phone (not shown) of operator 8596, and thus the cell phone becomes part of external communication system 8564, and the cell phone can initiate a call for help under the command of vehicle system controller 8552.
Though safety system process 8610 shows call for help process 8638 occurring after external vehicle warnings are initiated and after controller 8552 has taken control of vehicle 8550, if vehicle 8550 is configured to permit controller 8552 to have such control, call for help process 8638 may occur while initiate vehicle warnings process 8634 and control vehicle process 8636 are in process to enable the fastest emergency response possible to the condition of operator 8596.
Once call for help process 8638 is complete, safety system process 8610 has performed all the functions enabled in vehicle 8550 that permit warning other vehicle operators, controlling vehicle 8550 to a stop, or moving vehicle 8550 to the side of the road and then stopping vehicle 8550, and calling for help. Control then passes to a maintain conditions decision process 8640.
In maintain conditions decision process 8640, vehicle system controller 8552 will maintain vehicle 8550 in a stopped condition with external warnings continued until either fuel and battery power are depleted, until vehicle 8550 is turned off, or until override switch 8578 is actuated. If any condition exists that indicate maintaining warnings, maintain conditions decision process 8640 will loop back on itself. If a power off or fuel and battery power depleted condition occurs, or if the condition that led to warnings and control has been overridden or reset, control may return to any previous point in safety system process 8610. In an exemplary embodiment, control passes from maintain conditions decision process 8640 to continue operating vehicle decision process 8624, and operation of vehicle safety process 8610 continues as previously described.
While this disclosure provides significant information regarding apparatus for measuring the temperature at the skin adjacent to, over, or on the brain thermal tunnel or ABTT, ultimately the value and benefit of ABTT measurements is for monitoring, diagnosis, and treatment of patients or subjects. In the following paragraphs are exemplary embodiments of applications of ABTT measurements, which may be made by the apparatus disclosed herein or by other apparatus appropriately configured to locate and measure the skin at the ABTT terminus.
As described herein, measures of body core temperature may not reflect brain temperature and, certainly, are not suited for detecting rapid changes in brain temperature. Use of an embedded hypothalamic probe in sheep has identified changes in hypothalamic temperature disproportionate to those of intracarotid and rectal probes. Applicant has established that a surface sensor placed on the skin of the SMO and eyelid overlying a “brain thermal tunnel” (ABTT), to the cavernous sinus constitutes an effective means for continuous noninvasive assessment of intracranial brain temperature. Applicant tested whether ABTT monitoring via a surface probe on the skin at the ABTT terminus (e.g., see
Over 200 patients and healthy subjects participated in the studies. By way of illustration, equally calibrated temperature sensors were placed or positioned on the SMO skin of six subjects. Five of the subjects also had a temperature sensor positioned on the skin over the temporal artery of the forehead. The sixth subject had a rectal thermometer probe positioned to measure rectal temperature. Simultaneous readings in degrees Celsius were obtained at intervals ranging from 15 to 60 sec during sleep in a persistently dark room. All subjects urinated at least once during the study period to measure arousal or awakening; urination was into a urinal to avoid ambulation). Temperature increases and decreases were quantified during sleep onset, arousal from sleep, and awakening from sleep.
The results of testing show consistency with the decrease in metabolism that accompanies sleep. Referring to
Referring to
Monitoring at the ABTT terminus site with the apparatus disclosed herein revealed brain thermal information during sleep that was previously unknown, including the level of temperature, thermal patterns, thermal signatures, and thermal gradients. ABTT temperature monitoring, in accordance with this invention, was performed in two hundred subject and patients during sleep. Eighteen normal patterns were identified, and of those eighteen patterns, nine patterns showed the highest consistency of measurements (
By identifying ideal thermal patterns for sleep for optimizing immune function and reduction of sleep fragmentation, the present disclosure provides another embodiment that includes a method, apparatus and system for optimizing sleep (referred herein as a Sleep Optimization System, SOS), shown in
Once the thermal sleep pattern as measured by temperature monitoring system 8696 starts to depart from the ideal thermal sleep pattern, the thermal signal is recognized by controller 8698 (based on comparison of the received signal with predetermined values for ideal sleep stored in non-transitory memory 8700). Controller 8698 is configured to recognize the abnormal temperature signal and then to activate a wireless transmitter 8702 included as a part of temperature monitoring system 8696. In an exemplary embodiment, wireless transmitter 8702 is a near field communication transmitter with a relatively short range, such as Bluetooth or Wi-Fi. Wireless transmitter 8702 transmits a temperature signal to a wireless receiver 8704 of thermal actuator 8692. Thermal actuator 8692 is chosen based on the need to cool or warm a subject to achieve an ideal sleep pattern. Thermal actuator 8692 includes a controller 8706. Controller 8706 is configured to identify the need to heat or cool a body 8708. If body 8708 needs cooled rather than heated, controller 8706, in an exemplary embodiment controller 8706 communicates with a cooling system 8710 to provide cooling to body 8708. Thus, controller 8706 is able to command heating or cooling to best match the temperature curve slope of the ABTT terminus characterizing an ideal sleep pattern. Although the description hereinabove uses a wireless system for transmission, it should be understood that a wired connection can be used, and in an exemplary embodiment, a wire or cable 8712 of thermal actuator 8692 is connected to the temperature monitoring system 8698. On the other hand, if controller 8706 identifies a need for warming up the brain, then, for example, a contact thermal device 8714 such as thermal blanket is activated. Ideal sleep patterns include a decrease in brain temperature ranging from 0.8° C. to 2.9° C. from a baseline temperature, within a time period ranging from 59 minutes to 180 minutes, where baseline is the waking temperature at time zero. Ten preferred sleep temperature patterns include: (i) temperature drop of 2.0° C. within 59 min; (ii) temperature drop of 2.7° C. within 101 min; (iii) temperature drop of 2.1° C. within 150 min; (iv) temperature drop of 2.1° C. within 180 min; (v) temperature drop of 1.9° C. within 75 min; (vi) temperature drop of 2.8° C. within 135 min; (vii) temperature drop of 1.1° C. within 139 min; (viii) temperature drop of 0.8° C. within 100 min; (ix) temperature drop of 1.4° C. within 170 min; and (ix) temperature drop of 1.2° C. within 121 min (not in graph).
SOS System 8690 of the present disclosure includes controller 8698 in temperature monitoring apparatus 8696. Controller 8698 is configured to include instructions for the operation of temperature monitoring system 8696 and is operatively coupled to non-transitory memory 8700 and wireless transmitter 8702. In the embodiment of
Controller 8698 is configured to compare an acquired thermal pattern and slope to thermal patterns stored in the non-transitory memory 8700. Furthermore, controller 8698 is configured to identify an acquired thermal sleep pattern that departs from an ideal pattern stored in non-transitory memory 8700. If an abnormal pattern is detected, then controller 8698 activates wireless transmitter 8702 to send a signal to a thermal actuator 8714 or a cooling system 8710, as described herein. Thermal actuator 8692 includes a wireless receiver 8704, which is coupled to thermal actuator controller 8706. Controller 8706 adjusts thermal output up or down based on temperature data (thermal curve) received from temperature monitoring device or system 8696.
In an exemplary embodiment, a method of controlling the temperature of a body 8708 during sleep may include the following steps: (1) measuring temperature of the ABTT terminus (preferably at 1 Hz); (2) identifying a thermal sleep pattern (such as slope of the curve and/or the velocity of temperature drop) every 1 minute or less (or preferably every 30 seconds or less); it should be that any frequency of measurement ranging from every 10 minutes to every 1 second is within the scope of the disclosure, but the preferred embodiment uses the most frequent measurements possible; (3) although this next step is optional, controller 8698 may be configured to predict the final thermal pattern based on the slope acquired; in step (4) controller 8698 compares the acquired slope or thermal pattern with the predetermined ideal thermal pattern stored in non-transitory memory 8700; if in the next step (5) controller 8698 identifies a departure from ideal sleep pattern, then in next step (6) wireless transmitter 8702 of temperature monitoring system 8696 is actuated, with a signal transmitted to thermal actuator 8692; and (7) thermal actuator 8692 is configured to determine the amount of thermal adjustment needed to achieve ideal thermal sleep pattern (disclosed herein) by delivering, by way of illustration, heat, via a device such as contact thermal device 8714, or cold, such as by cooling system 8710, to body 8708 of a subject.
What is clear from
In contrast to forehead temperature 8222 and rectal temperature 8236, ABTT temperature 8220 and 8238 very precisely detected changes in brain metabolism associated with sleep onset 8224 and 8240, sleep arousal 8230 and 8242, and awakening 8232 and 8244. The ability to monitor sleep cycles in this manner provides a new and hitherto unknown capability to diagnose normal disturbed sleep cycle patterns. Furthermore, with ABTT temperature analysis, a new diagnostic tool is presented to analyze insomnia, catatonia, and coma, and determine whether recovery and treatment are possible and effective. Furthermore, because intensity of sleep is monitored, ABTT temperature analysis leads to effective assessment of depth of anesthesia, intraoperative awareness, intensity of anesthesia-induced coma, and normal progression of recovery from anesthesia. Perhaps even more importantly, ABTT temperature analysis is capable of determining when a brain is under critical stress indicative of a pre-death condition, which is currently not possible with conventional temperature measurement apparatus and methods.
Stated more clearly, measurement of the skin temperature at the ABTT terminus can predict when a patient or subject is moving from an awakened state to a pre-sleep condition by: (1) identifying an awake condition ABTT temperature 8254; (2) identifying a pre-sleep or drowsy condition by a sustained decline 8256 in ABTT temperature 8220 of at least 0.5° C.; and (3) identifying onset of a sleep condition by a precipitous decline 8258 in ABTT temperature 8220 of at least 0.2° C. in a period of approximately one minute. Further, an arousal condition 8230 during sleep can be predicted by monitoring ABTT temperature 8220 for a precipitous increase during arousal condition 8230 of at least 0.2° C. in a period of approximately one minute. Further yet, an awakening condition 8232 can be predicted by monitoring ABTT temperature 8232 for an increase in ABTT temperature of at least 0.7° C. from a minimum temperature recorded during a sleep cycle in a period of five minutes or less. The dramatic improvement in the present system and apparatus is that such predictions of sleep progression are made in advance of even the patient or subject knowing that they are become aroused or awake. Indeed, the patient or subject may be completely unaware of an aroused state, but by monitoring an ABTT temperature, such conditions may be more than recognized, they may be accurately predicted.
The consequence of predicting arousal and awakening are significant in a variety of circumstances. When a patient is under anesthesia, for example, an arousal state corresponds to inadequate anesthesia. Furthermore, an awakening state during a medical procedure, which rarely happens, can readily be predicted by identifying an awakening condition 8232 from ABTT temperature 8220, and applying additional anesthetic to restore a patient to a sleep condition.
Additionally, the ability to sense drowsiness has implications for maintaining an awakened state. For example, if a drowsy state is identified by sustained decline 8256, a device, such as a loud tone, a mechanical vibration, or the like, can restore a subject to a full awakened condition before sleep occurs. Broadly, because changes in the ABTT temperature precedes the actual onset of a drowsiness, sleep, arousal, and awakening, these conditions may be used to predict the actual condition and the impending condition may be prevented, if such is desirable in a specific environment.
It should be noted that current determination of sleep condition in sleep studies requires positioning of sensors in a plurality of locations on a patient, each sensor connected by a wire that is non-conducive to sleep and non-conducive to sustained sleep. Furthermore, such sensors can be invasive, sometimes requiring shaving of skin in multiple locations. Still further, diagnosticians often do not know the patient is awake until the patient is actually awake, in contrast to ABTT temperature, which begins generating heat in the brain to provide a sort of “firing up” of brain systems in anticipation of being awake. Similarly, heat is generated in the ABTT as part of arousal, though less than is needed for waking, because the needs of body systems is less than for waking. Thus, the benefits of ABTT temperature monitoring for sleep in any environment is more accurate than conventional techniques, is predictive, and is minimally invasive, replacing hordes of wires and sensors in some circumstances.
The last step can be used when the sleep onset detector is used to alert the user about sleep onset, such as when driving, operating machinery, and for any other situation that the user needs to remain awake. In situations in which the user does not need to be awakened or alerted, sleep onset detector 8720 does not activate reporting apparatus 8732, and in this case, sleep onset detector 8720 is used to identify abnormal sleep patterns, disease patterns, or changes in physiology such as ovulation. Sleep onset detector 8720 can include an adhesive surface 8734, and has a length of at least 1 inch to position one sensor over the ABTT and the second sensor on the forehead skin. Although a second sensor adapted to measure temperature on the forehead is described, it should be understood that a second sensor measuring temperature in any body cavity (such as mouth, rectum, bladder, esophagus) or on any surface of the face (such as cheek, mouth, and the like), surface of the head and neck (such as retro-auricular and the like), or surface of the body (e.g., chest, shoulder, arm, hands and the like) can be used, and such a temperature measurement for comparison is in accordance with the scope of this invention. It should also be understood that although an adhesive-based embodiment of sleep onset detector 8720 is described, any other temperature detector containing at least two thermal sensors can be used to measure the temperature of the ABTT terminus site and other skin location, and are within the scope of this disclosure. Exemplary embodiments of sleep onset detector 8720 include: One physical unit 8720 as shown in
As previously described herein, monitoring core brain temperatures is beneficial for understanding brain reaction in a surgical environment. Recent surgical care improvement program (SCIP) criteria include attempting to maintain perioperative core temperature at >36° C. One of the most difficult aspects of complying with such guidelines is the limitation of current means of thermometry. Invasive monitoring is restricted to limited settings, i.e., rectal, forehead, oral, and armpit, and may not be readily transferred between settings. Besides being limited by the difference to actual core temperature, skin monitoring is distorted by anesthesia and changes in room or ambient temperature. As described herein, Applicant has unexpectedly found through significant research and testing that the superior medial orbit, or SMO, and medial eyelid area, typically sustains the highest temperature on the body surface, absent ambient temperatures higher than SMO, and measures core temperature without need for an offset or correction factor. As described herein, the SMO site overlies the brain thermal tunnel or ABTT, an insulated pathway between the SMO and the perihypothalamic region located in a central portion of the brain. Applicant undertook significant research to understand the consistency of ABTT terminus temperature readings in the context of two potentially disruptive settings: patients or subjects exposed to an operating room environment after induction of anesthesia, and cattle exposed to extremes of temperature. Applicant unexpectedly found through research and testing that monitoring skin temperature over the brain thermal tunnel was unaffected by changes in ambient temperature in humans undergoing surgery and cattle exposed to extremes of temperature.
ABTT adhesive thermal or temperature sensors were placed on the skin of the SMO of ten cardiac patients during median sternotomy prior to cardiopulmonary bypass. Simultaneous measurements were obtained of the temperature of the Pulmonary Artery (PA) and ABTT 8140 after insertion of a PA catheter and 40 minutes later, during which interval the patient was exposed to an operating room temperature of approximately 13° C.
Additionally, the similarity of ABTT 8140 temperature to the standard measure of core temperature in animals and the impact of changes in ambient temperature were assessed in four cattle at two-hour intervals in a climate-controlled chamber while chamber temperature was changed between 20° C. and 36° C. over the course of 140 hours.
The results of the patient data indicate that, at the onset of PA catheter measurements, the average PA-ABTT temperature difference was 0.08±0.12° C. At 40 minutes, the mean PA-ABTT temperature difference was 0.16±0.13° C. In other words, averaged ABTT temperature is measurably as well as statistically indistinguishable from pulmonary artery temperature.
Referring to
The data in
As described herein, the measurements of skin temperature at the ABTT terminus provides multiple advantages in a variety of settings. One such type of setting is one in which the brain is at increased risk for hyperthermic injury, ranging from patients undergoing hypothermic cardiac bypass (hCPB) to cerebral protection for active athletes and soldiers in a warm environment. Extreme changes in core temperature can result in a severe reduction and ultimately cessation of metabolic functions. Such extreme changes in core temperature are the case when hypothermia or hyperthermia occurs. These thermal disturbances can be life-threatening if not diagnosed or properly treated.
As described herein, with the discovery of the ABTT core body temperature can be monitored continuously and noninvasively. Measurements of temperature on the skin over, adjacent to, or on the ABTT terminus with a surface sensor on the superomedial orbit correlate highly with established core readings during steady states, as described herein. Thus, the ABTT may be beneficially used to measure the temperature of patients during cardiopulmonary bypass and the temperature of athletes, workers in any adverse temperature environment, and soldiers during exercise by identifying brain temperature instead of core temperature.
As described herein, measurements of skin temperature over, adjacent to, or on the brain thermal tunnel or ABTT with a surface sensor on the superomedial orbit and eyelid correlate highly with established core readings during steady states. Of potential value is measuring the core temperature during medical procedures, such as surgery.
Applicant has shown that a thermal sensor on the skin of the superomedial orbit and eyelid, overlying the brain thermal tunnel, provides reliable assessment of core temperature during steady state conditions in healthy volunteers and patients under anesthesia. Ongoing anatomical studies indicate that ABTT anatomy enables a surface monitor to be in virtual continuum with an insulated passage to the cavernous sinus; and Applicant has proven that ABTT is reflective of intracranial and brain temperature. We therefore applied a thermal sensor to the skin overlying the ABTT during hypothermic cardiopulmonary bypass (hCPB) and compared it to changes in core blood.
In a research study, a ABTT thermal sensor at the end of a plastic wing anchored by adhesive to the forehead, similar to temperature sensor 8002 (see
During pre-bypass phase 8290, it was confirmed that the mean ABTT temperature (34.9±0.4° C.) was similar to pulmonary artery temperature (PA, 35.1±0.5° C.) and esophageal temperature (34.8±0.5° C.—not shown). Applicant compared the relationship of ABTT temperature 8262 to these measures of core as well to oxygenator inflow (not shown) and oxygenator outflow (not shown) after onset of bypass and at their respective troughs.
The results in
These studies suggest that although the skin at the ABTT terminus provided readings comparable to established measures of core temperature under steady-state and slowly changing conditions, it evidenced decoupling from core temperatures during cooling for hCPB. This research highlights the potential to overestimate the speed at which cooling provides brain protection.
The results show that during hCPB, in a period 8270 prior to rewarming, ABTT terminus temperature 8262 cooled to a slightly lesser degree hCPB than PA temperature 8264, esophageal temperature (not shown in
These studies indicate that the greater ABTT temperature 8262 measured towards the end of rewarming 8276 is evidence that ABTT temperature is uniquely sensitive to brain metabolism and may constitute a noninvasive measure of brain temperature that is vital to prevent hyperthermia-induced and/or hyperthermia-exacerbated neurocognitive injury in this context.
Furthermore, during the initial cooling period 8278, measured ABTT temperature 8262 was substantially higher than PA temperature 8264, which has significant implications for proper cooling of patients during certain medical procedure. Therapeutic hypothermia is believed to reduce the risk of brain tissue injury due to the lack of blood flow by decreasing oxygen demand in the brain, reducing production of neurotransmitters, and reducing free radicals. Currently, PA temperature 8264 is used as an indicator of brain temperature. However, as shown in
Accordingly, the ability to measure temperature of the ABTT terminus during a medical procedure leads to an improved ability to establish proper therapeutic hypothermia and/or hyperthermia and to prevent tissue destroying hyperthermia and life-threatening hypothermia. More specifically, such a procedure may be accomplished in an exemplary embodiment by a temperature modifying apparatus that includes (1) positioning a temperature sensor on the skin adjacent to, over, or on the ABTT terminus; (2) applying cooling or heating to a patient or subject; and (3) when the ABTT terminus indicates brain temperature has reached a predetermined target level, change from a temperature modifying (either increasing or decreasing) operation to a temperature maintenance operation. To specifically provide appropriate warming or re-warming from a cooled condition using an existing or properly positioned ABTT terminus temperature sensor, (1) remove any remaining cooling apparatus; (2) begin rewarming protocol; (3) monitor brain temperature response by monitoring the slope of ABTT temperature increase during initial warming; (4) when the ABTT temperature reaches a first predetermined target warming temperature, which in an exemplary embodiment may be 35° C., begin reducing warming procedures; (5) when the ABTT temperature reaches a second predetermined target warming temperature, which in an exemplary embodiment may be 36.5° C., cease all warming procedures; and (6) if ABTT temperature moves into a hyperthermic temperature range, which in an exemplary embodiment may be above 37.0° C., reintroduce cooling protocol to reduce or prevent neural damage due to hyperthermia; (7) otherwise, cease all warming and cooling protocols.
An exemplary embodiment of therapeutic hyperthermia may be accomplished through a similar technique, by (1) positioning a temperature sensor to measure the temperature of the skin adjacent to, over, or on the ABTT terminus; (2) begin a hyperthermia warming protocol; (3) monitor brain temperature response by monitoring the slope of ABTT temperature increase during initial warming; (4) when the ABTT temperature reaches a first predetermined target warming temperature, begin reducing warming procedures; (5) when the ABTT temperature reaches a second predetermined target warming temperature, cease warming protocol and, if appropriate, change to an elevated temperature maintenance protocol; and (6) if ABTT temperature moves beyond the target temperature, cease warming protocols and introduce gradual cooling to the body trunk.
It should be noted that the target temperatures for therapeutic hyperthermia or hypothermia varies based on the purpose of the treatment. Furthermore, because conventional temperature measurements are unreliable, target temperatures may need to be adjusted, and can be adjusted, given the ability to accurately measure brain temperature at the ABTT terminus. Further yet, all temperatures that are “normal” or “baseline” should be for a particular subject or patient, given the normal variation of temperatures for humans. Thus, any changes in temperature are not absolute, but are tailored to the normal temperature of an individual.
Once therapeutic hyperthermia is completed, cooling of the patient or subject to normal temperatures may occur. Because therapeutic hyperthermia provides relatively small temperature elevation, ambient temperature is normally sufficient to return the patient to a normal temperature. Continuous monitoring of the ABTT terminus is important during cooling to normal temperature to prevent the brain for compensating for cooling by generating heat through shivering or other techniques. It is generally accepted procedure to incorporate an anti-shiver mechanism in therapeutic hypothermia. Such mechanism may be, for example, one or more drugs for suppressing a shiver response. However, shivering may also be limited by heating extremities (hands and feet) while cooling the body trunk. Generally, exemplary cooling is accomplished by (1) positioning a temperature sensor to measure the temperature of the skin adjacent to, over, or on the ABTT terminus; (2) provide an ambient temperature no greater than approximately 27° C., and no less than approximately 19° C.; (3) depending on the reaction of the ABTT temperature in response to cooling, it may be necessary to slow the rate of cooling by adding insulation or a slight amount of heating to the patient; and (4) once a ABTT target temperature is reached, which in an exemplary embodiment is approximately between 37.5° C. and 38.0° C., reduce the rate of cooling and begin to change to a temperature maintenance protocol.
Currently the level of temperature of the blood (or fluid) being delivered to the patient, called inflow, is chosen in a random manner because there is no way to know what the temperature of blood should be to accomplish cerebral cooling. Likewise, currently there is no method to predict exactly the duration of infusion of cold blood (or duration of inflow). By measuring the temperature of the skin on, over, or adjacent the ABTT terminus in over 200 patients undergoing surgery, Applicant has identified the thermal pattern that provides answers to both of those questions: (a) temperature level of the blood (or fluid) being infused (i.e., inflow temperature), and (b) duration of time delivering fluid (i.e., time of inflow). In accordance with the principles of the present disclosure, as shown in
Automated warming-cooling system 8770 includes a temperature measuring device 8772 and a thermal actuator 8774, which in an exemplary embodiment may be an oxygenator or bypass machine. In the exemplary embodiment of
Controller 8776 is configured to calculate the temperature of flow or inflow, the inflow temperature being presented on reporting apparatus 8782 of temperature measuring device 8772. In the embodiment of
Baseline temperature at the ABTT site provides the basis for determining the temperature of inflow fluid, said inflow fluid temperature being 15° C. lower than the ABTT terminus baseline temperature, and more preferably in the range 15° C. and 25° C. lower than the ABTT terminus baseline temperature, and yet more preferably 25° C. lower than ABTT terminus baseline temperature, when ABTT terminus baseline temperature is within levels between 35° C. and 37° C. Likewise, when there is a predetermined drop in temperature from the baseline, inflow should cease since the duration of inflow and temperature of the inflow fluid will reach the brain cooling effect, which is predicted by the apparatus 8770, said prediction based on the temperature drop from baseline and slope of the curve corresponding to the drop of temperature, said controller or processor 8776 being adapted to continuously identify change in the temperature measured and compare to the baseline temperature stored in non-transitory memory 8778.
When controller 8776 identifies a temperature drop in the range of 10° C. to 18° C. at the ABTT terminus site compared to baseline, and more preferably a temperature drop in the range of 13° C. and 16° C. at the ABTT terminus site compared to baseline, controller 8776 activates a stop mechanism at the thermal actuator or oxygenator 8774, so as to stop inflow of cold fluid.
Likewise, controller 8776 is configured to perform a similar function for warming. When there is a predetermined increase in temperature from the ABTT terminus baseline, inflow of warm fluid should cease since the duration of inflow and temperature of the inflow fluid will reach the desired brain warming effect, which is predicted by automated heating-cooling system 8770, said prediction based on the increase of temperature from ABTT terminus temperature baseline and slope of the curve corresponding to the increase of temperature, controller 8776 being adapted or configured to continuously identify change in temperature measured and compare to the baseline temperature stored in non-transitory memory. When controller 8776 identifies a temperature increase between 4° C. and 11° C. at the ABTT site compared to baseline, and yet more preferably a temperature increase between 6° C. and 9° C. at the ABTT site compared to baseline temperature, controller 8776 is configured to actuate a stop mechanism at thermal actuator or warming machine 8774, so as to stop inflow (or heat transfer for warming using any other device), and thereby prevent damage due to brain overheating, also called hyperthermia.
It should be understood that the ABTT terminus baseline can be the initial temperature of the patient, but other baselines can be used, such as the no-flow phase of cardiac bypass surgery, the no-flow baseline being used by controller 8776 being configured to use the no-flow baseline to control heating or cooling of blood inflow. Alternatively, the ABTT terminus baseline is the lowest temperature achieved prior to executing the warming function by controller 8776.
Thermal actuator 8774 includes any device or article of manufacturing that can warm or cool a body, by contact or non-contact means, and by way of illustration, any warming or cooling system that delivers air or fluid to the body and any article of manufacturing that can exchange temperature with the body by contact through warming or cooling any part of the body.
Therapeutic hypothermia and hyperthermia may provide significant benefit in the treatment of certain diseases and conditions. However, such therapies also present a risk of brain damage. The accurate and fast measurement of brain temperature at the skin on the ABTT terminus and characterization of slope that exceeds a predetermined slope pattern, as disclosed herein, reduces the risk of such therapies to the brain by “listening” to the brain. It should be apparent from the foregoing description that the use of non-invasive ABTT terminus temperature measurements during therapeutic hypothermia and therapeutic hyperthermia is a significant improvement over conventional approaches to measuring analogs for brain temperature.
As yet another embodiment of the present disclosure, research was conducted on volunteers during exercise. As shown in
Accordingly, a first exemplary embodiment thermal injury susceptibility may be measured by a brain temperature response function (BTRF) during exercise in any environment, but most particularly an environment with an elevated temperature. The BTRF is broadly a change in brain temperature in response to any stimulus, either external or internal. In an exemplary embodiment, such a measurement of BTRF may include (1) providing an environment with an elevated temperature, for example, 35° C.; (2) establish a nominal ABTT temperature condition prior to exercise or entry in the heated environment; (3) place the subject in the heated environment; (4) measure the BTRF in the heated environment; (5) initiate exercise activities if appropriate to the subject and the initial BTRF response; and (6) cease all activities when the subject's BTRF reaches a predetermined temperature, for example 39.0° C. and place the subject into an environment with a temperature approximately nominal room temperature. Be wary of cooling the patient too rapidly, which may generate an adverse effect by causing the body to believe it is becoming excessively cool, causing shivering or other adverse reactions. Measurement of the ABTT temperature must be maintained throughout the process. The BTRF determines the ability of the subject to function in an environment with an elevated temperature without permanent injury. It should be understood that the BTRF can be used in other applications, including, but not limited to, surgery as described herein in which a patient is cooled and warmed, or any other procedure for cooling or warming the body and brain.
As a second exemplary embodiment, such monitoring may be accomplished during exercise in a non-heated environment to monitor brain temperature and keep such temperature from reaching damaging levels. In an exemplary embodiment, such a measurement of BTRF may include (1) establish a nominal ABTT temperature condition prior to exercise; (2) initiate exercise activities appropriate to the subject and the initial BTRF response; and (3) cease all activities when the subject's BTRF reaches a predetermined temperature, for example 39.0° C., or if the slope of the BTRF exceeds a predetermined slope, for example, a BTRF slope steeper or greater than approximately 0.07° C./minute, and place the subject into an environment with a temperature approximately nominal room temperature. As before, be wary of cooling the patient too rapidly, which may generate an adverse effect by causing the body to believe it is becoming excessively cool, causing shivering or other adverse reactions. Measurement of the ABTT temperature must be maintained throughout the process. In this particular case, the function of the BTRF is to assure that exercising is performed in a thermal regime that is non-damaging to the brain. For example, obese individual moving heavy objects continuously even in relatively cool weather may see a BTRF that exceeds a dangerous level, leading to an adverse systematic response, including coma, heart attack, and, in the most extreme cases, death. However, measurement of ABTT temperature permits calculation of a BTRF, and ultimately an acceptable or safe BTRF for any individual.
While the various embodiments of measuring the ABTT temperature and graphing that temperature in a BTRF provides many advantages over conventional temperature measurements, particularly when coupled with specific situations, including surgery, anesthesia, exercise, sleep, etc., an entirely unexpected result occurred in a frequency analysis of the temperature at the skin of the ABTT terminus.
In the prior art, thermoregulation has not been assessed by changes in body temperature because of the inability to measure brain temperature; instead, investigators relied, and still rely, on changes in cardiovascular signals. The development of temperature sensors and monitoring equipment described herein that enabled capturing of thermal signals at a rate faster than thermal band frequencies enabled assessment of thermal variability, and thereby enabled assessment of the nonlinear dynamics of thermoregulation. ABTT technology is applicable to a unique, hitherto unknown system for measuring the health of individuals.
In an ongoing series of studies, Applicant employed ABTT sensors that recorded temperature as frequently as q15sec at the forehead, rectum, and at the skin of the ABTT terminus. As described herein, the results of the ABTT temperature sensor showed the greatest time variability, suggesting plasticity of the thermoregulatory system that is not appreciated by monitoring at a site remote from the hypothalamus, e.g., the rectum.
It has been noted that, despite the potential utility of assessing temperature variations to predict morbidity, all too often temperature is viewed as a dichotomous variable (fever/no fever). The present findings open new avenues of research with respect to thermal and thermodynamic phenomena. The assessment of temperature as disclosed herein enables better understanding of thermoregulatory control during health, as well as disease, and during normothermia as well as hypothermia, hyperthermia and fever. To this end, Applicant connected a spectrum analyzer 8177 to BTT system display 8001. More specifically, controller 8112 provided temperature data to spectrum analyzer 8177. The present data were collected at 15 sec. Greater spectral resolution will be attainable with new probes that sample as rapidly as 1 Hz.
Additionally, the symmetry of peaks 8287 and 8289 located at the left or low frequency end of line 8292 and the right or high frequency end of line 8292 also relate to the health of an individual, with nearly perfect symmetry indicative of a healthy individual, and asymmetric peaks, either by frequency position or amplitude, is indicative of a less healthy person, or, when the peaks begin deviating from each other, a person with a medical condition. Such condition should be suspected when peaks 8287 and 8289 are asymmetric by 5% or more, and such condition is likely when peaks 8287 and 8289 are asymmetric by 10% or more.
Accordingly, a diagnostic system enabled by frequency analysis is enabled by ABTT temperature measurement. In an exemplary embodiment, the system includes: (1) monitoring ABTT temperature with the fastest temperature sensor available for a time interval, for example, an hour; (2) converted the received temperatures to a frequency response through a spectrum or frequency analyzer 8177; (3) determine the mean interval between peaks and the slope of the peaks across the central portion of the frequency spectrum. If the mean interval between peaks is more than a predetermined amount greater than the mean interval between peaks for a healthy individual of a similar age, for example, 10%, or more than 0.007 Hz, then a medical condition or disease could be at work and further diagnosis may warranted. Similarly, if the slope of the peaks deviates from a horizontal line by a predetermined amount, such as a slope greater than −0.03power/Hz, a disease or medical condition should be suspected.
It should be understood that an exemplary embodiment of the apparatus described herein includes a controller or processor, a non-transitory memory, and a reporting apparatus, such as a display, audible or written output, etc. The controller is operatively coupled to the non-transitory memory, and the controller is configured to analyze data captured by an ABTT temperature sensor and to compare the analyzed data to pre-determined information, such as, by way of example, temperature levels, temperature variation in a certain time, slopes, and the like, stored in non-transitory memory. The controller is configured to compare the acquired and analyzed temperature data with the data stored in non-transitory memory, and when there is an identified analytical match, i.e., the data matches predetermined ratios or percentages or predetermined profiles, the reporting apparatus reports, displays, signals, prints out, or otherwise provides notification of the identified match.
Applicant has determined, through experimentation, that finding the precise location of the skin location overlying the ABTT terminus can be accomplished relatively quickly with a properly training and experienced individual. However, in some circumstances it may be difficult to locate the location of the ABTT terminus rapidly. For example, during an emergency, dim light conditions, and other circumstances, it may be challenging to find the skin location of the ABTT terminus. Accordingly, Applicant has developed various apparatuses to improve the ability to find the skin location of the ABTT terminus.
When using any of temperature sensors 8002, 8004, 8006, or 8008, typically the sensor will be moved back and forth over the skin in the area of the ABTT terminus. When locating the ABTT terminus in typical room temperature conditions, the temperature scans provide temperature outputs that appear similar to those presented in
As described hereinabove, under certain circumstances, it may be challenging to locate the center of the ABTT terminus.
ABTT terminus location process 8300 begins with a start process 8302, where registers may be reset to zero, any predetermined values may be loaded, and other initializations may occur. Once start process 8302 is complete, control passes from start process 8302 to an initiate learn/acquisition mode process 8304.
In initiate learn/acquisition mode process 8304, ABTT monitoring system 8000 provides power to a temperature sensor and prepares to acquire data from the temperature sensor. ABTT monitoring system 8000 may perform other activities in initiate learn/acquisition mode process 8304, such as uploading from non-transitory memory 8114 a program to analyze temperature data, setting aside memory to store temperature data in non-transitory memory 8114, etc. Once initiate learn/acquisition mode process 8304 is complete, control passes to a receive temperature data process 8306.
In temperature data process 8306, ABTT monitoring system 8000 receives a plurality of data points that represent the temperature of the skin in the area adjacent to, over, or on the ABTT terminus. The temperature data is stored in memory in ABTT monitoring system 8000, which may be non-transitory memory 8114. Once a plurality of data points have been received, control passes from temperature data process 8306 to an analyze temperature data process 8308.
In analyze temperature data process 8308, a virtual representation of the temperatures of the ABTT terminus is created, which may appear similar to the three-dimensional graph of
In change sensitivity process 8310, the sensitivity of the ABTT monitoring system 8000 is changed from standard, approximately linear sensitivity, where all temperatures are read, to a cutoff sensitivity, wherein temperatures below a certain value are no longer considered in locating the position of the ABTT terminus. Such change in sensitivity behaves functionally in a manner similar to that shown in
The function of change sensitivity process 8310 is aid a user in finding the location of ABTT terminus 8140. Once a user has scanned the area of ABTT terminus 8140 in learn/acquisition mode process 8304, and once ABTT monitoring system 8000 has identified peak or high temperature 8334, in analyze temperature process 8308, the need is for ABTT monitoring system 8000 to tell the user where peak or high temperature 8334 is located. A coronal temperature 8336 surrounds ABTT terminus 8140, and the coronal temperature may make it hard to find peak temperature 8334. By reducing the sensitivity of ABTT monitoring system 8000 in change sensitivity process 8310, using peak temperature 8334 as a basis, the search area is greatly reduced, making the center of ABTT terminus 8140 easier to location. Once the sensitivity of ABTT monitoring system 8000 has been modified, control passes to a receive temperature data process 8312.
In receive temperature data process 8312, temperature data from a temperature sensor is received by ABTT system display 8001, where the temperature data is analyzed. Once the temperature data has been received and analyzed, control passes to a high temperature decision process 8314.
In high temperature decision process 8314, ABTT terminus location process 8300 determines whether the received temperature data is higher than the current high temperature identified in analyze temperature data process 8308. If the received temperature data is higher or greater than the current high temperature, control passes from high temperature decision process 8314 to an analyze existing data process 8316.
In analyze existing data process 8316, any existing temperature curve is analyzed in view of the newly received temperature data. ABTT terminus location process 8300 may determine that the higher temperature appears, by analysis, to be the actual high temperature. Alternatively, ABTT terminus location process 8300 may determine that the temperature curve data indicates a higher temperature may be available. Once the newly received temperature data is analyzed, control passes from analyze existing data process 8316 to a temperature consistency decision process 8318.
In temperature consistency decision process 8318, based on the analysis provided by analyze existing temperature data process 8316, ABTT terminus location process 8300 decides whether the newly received high temperature is consistent with the existing temperature map as a peak temperature of the ABTT terminus. If the newly received data appears to be consistent with the temperature map, control passes from temperature consistency decision process 8318 to an actuate indicator process 8320, which an indicator of ABTT monitoring system 8000 is actuated to indicate the ABTT terminus high temperature has been located. Such indicators may include tones, flashing displays, and/or other visual, vibrational, or audio indications on ABTT system display 8001. Alternatively, an indication may be provided on the temperature sensor. In an exemplary embodiment, LED's 8088 shown in
Returning to temperature consistency decision process 8318, if the new high temperature is not consistent with the current temperature map, control is passed from temperature consistency decision process 8318 to received temperature data process 8312, and ABTT terminus location process 8300 functions as previously described.
Returning to high temperature decision process 8314, if the temperature data is not higher than the high temperature, control passes from high temperature decision process 8314 to a high temperature located decision process 8324. In high temperature located decision process 8324, ABTT terminus location process 8300 decides whether the current temperature data is at or near the identified high temperature. In an exemplary embodiment, if the temperature data is within 0.2 degrees Celsius of the peak temperature, ABTT monitoring system 8000 may consider the current temperature data to be close enough to peak ABTT temperature 8334 to consider the present temperature to be the peak, in which case, control passes from high temperature located decision process 8324 to actuate indicator process 8320, which functions as previously described. Alternatively, control passes from high temperature located decision process 8324 to receive temperature data process 8312, where ABTT terminus location process 8300 functions as previously described.
While ABTT terminus location process 8300 appears to be lengthy process, in practice, the learn/acquisition mode generally occurs within 5 to 30 seconds, and locating the ABTT peak temperature typically occurs in another 5 to 30 seconds. Thus, the entire process, from start to finding the peak ABTT terminus temperature, occurs in approximately 10 to 15 seconds, but may vary between 10 to 60 seconds.
Indicators on temperature sensors, such as LED's 8088 shown in
Another exemplary temperature sensor that provides a different apparatus for detecting the center of the ABTT terminus is shown in
Another exemplary embodiment temperature sensor is shown in
ABTT acquisition process 8380 begins with a start process 8382, where registers may be reset to zero, any predetermined values may be loaded, and other initializations may occur. Once start process 8382 is complete, control passes from start process 8382 to an initiate learn/acquisition mode process 8384.
In initiate learn/acquisition mode process 8384, ABTT monitoring system 8000 provides power to temperature sensor 8366 and prepares to acquire data from temperature sensor 8366. ABTT monitoring system 8000 may perform other activities in initiate learn/acquisition mode process 8384, such as uploading from non-transitory memory 8114 a program to analyze temperature data, setting aside memory to store temperature data in non-transitory memory 8114, etc. Once initiate learn/acquisition mode process 8384 is complete, control passes to a receive temperature data process 8386.
In temperature data process 8386, ABTT monitoring system 8000 receives a plurality of data points that represent the temperature of the skin in the area adjacent to, over, or on the ABTT terminus. The temperature data is stored in memory in ABTT monitoring system 8000, which may be non-transitory memory 8114. Once a plurality of data points have been received, control passes from temperature data process 8386 to an analyze temperature data process 8388.
In analyze temperature data process 8388, a virtual representation of the temperatures of the ABTT terminus is created in ABTT monitoring system 8000, which may appear similar to the three-dimensional graph of
In changing the mode of ABTT monitoring system 8000 from the learn mode, which system 8000 may indicate to a user by a tone, a display indication, a temperature sensor indication, such as flashing LED's 8370, or by other techniques or apparatus, to the seek mode, system 8000 is indicating to the user that system 8000 has sufficient data to identify and find the approximate center of the ABTT terminus. More specifically, system 8000 is indicating that it is able to find the peak, or near peak, temperature of the ABTT terminus. Once the mode of ABTT monitoring system 8000 changes to the seek mode, and advises the user that the mode has changed, control passes from change mode to seek process 8390 to a receive temperature data process 8392.
In receive temperature data process 8392, temperature data from temperature sensor 8366 is received by ABTT system display 8001, where the temperature data is analyzed. Once the temperature data has been received and analyzed, control passes to a high temperature decision process 8394.
In high temperature decision process 8394, ABTT terminus location process 8300 determines whether the received temperature data is higher than the current high temperature identified in analyze temperature data process 8308. If the received temperature data is higher or greater than the current high temperature, control passes from high temperature decision process 8394 to a reset temperature scale process 8396.
In reset temperature scale process 8396, the peak temperature is used to reset the temperature scale based on the new high temperature. In other words, the previous high temperature is replace by the new high temperature, after which control passes from reset temperature scale process 8396 to an analyze existing data process 8398.
In analyze existing data process 8398, any existing temperature curve is analyzed in view of the newly received temperature data. ABTT acquisition process 8380 may determine that the higher temperature appears, by analysis, to be the actual high temperature. Alternatively, ABTT terminus location process 8380 may determine that the temperature curve data indicates a higher temperature may be available. Once the newly received temperature data is analyzed, control passes from analyze existing data process 8398 to a temperature consistency decision process 8400.
In temperature consistency decision process 8400, based on the analysis provided by analyze existing temperature data process 8398, ABTT terminus location process 8380 decides whether the newly received high temperature is consistent with the existing temperature map as a peak temperature of the ABTT terminus. If the newly received data appears to be consistent with the temperature map, control passes from temperature consistency decision process 8400 to an actuate indicator process 8402, where all LED's 8370 are actuated to indicate that the ABTT terminus high temperature has been located. In addition to LED's 8370 being actuated, other indicators may be actuated, including tones, flashing displays, and/or other visual indications on ABTT system display 8001. Once actuate indicator process 8402 has actuated at least LED's 8370, control passes from actuate indicator process 8402 to an end process 8404, where ABTT terminus location process 8380 stops operation and passes control back to a calling program or other process of ABTT monitoring system 8000.
Returning to temperature consistency decision process 8400, if the new high temperature is not consistent with the current temperature map, control is passed from temperature consistency decision process 8400 to receive temperature data process 8392, and ABTT terminus location process 8380 functions as previously described.
Returning to high temperature decision process 8394, if the temperature data is not higher than the high temperature, control passes from high temperature decision process 8394 to an indicate direction of ABTT process 8406. In indicate direction of ABTT process 8406, LED's or lights 8370 that point along a direction where the ABTT terminus should be are illuminated. While ABTT monitoring system is able to determine the line along which the ABTT should be located, it is unable to indicate definitively which of the two possible directions temperature sensor 8366 should be moved to be in a direction that is toward the ABTT terminus. However, a user can easily determine the proper direction by visual inspection and/or moving temperature sensor 8366 in the indicated direction during the next back and forth movement or scan of temperature sensor 8366. Once the direction of the ABTT terminus is indicated, control passes from indicate ABTT direction process 8406 to a high temperature decision process 8408.
In high temperature decision process 8408. In high temperature decision process 8408, ABTT terminus location process 8380 decides whether the current temperature data is at or near the identified high temperature. In an exemplary embodiment, if the temperature data is within 0.2 degrees Celsius of the peak temperature, ABTT monitoring system 8000 may consider the current temperature data to be close enough to peak ABTT temperature 8334 to consider the present temperature to be the peak, in which case, control passes from high temperature decision process 8408 to actuate indicator process 8402, which functions as previously described. Alternatively, control passes from high temperature decision process 8408 to receive temperature data process 8392, where ABTT terminus location process 8380 functions as previously described.
While it appears that process 8406 and 8402 may yield confusing information, with two lights going on, followed by four lights when the ABTT terminus is located, in practice the two lights are kept illuminated until new information changes the direction of motion needed for the temperature sensor, so the movement of the temperature sensor toward the ABTT terminus until all lights illuminate is readily perceived as being natural.
Furthermore, the aforementioned process if very fast in comparison to most processes used to find ABTT terminus 8140. In actual use, ABTT terminus 8140 may be identified within seconds using temperature sensor 8366 and ABTT acquisition process 8380. A properly trained operator or user is typically able to find the ABTT terminus according to the system and method of this embodiment in no more than 15 seconds, and often in much less time.
It has been well documented that hot climate can strongly affect animal bioenergetics, with negative effects on livestock performance and welfare. High temperatures and acute heat loads on the homoeothermic animal depress feeding intake and affect animal performance like growth, milk and meat production as well as fertility. Capturing early animal responses to environmental challenges is very crucial to the livestock managers for adopting the right husbandry practices to reduce losses during hot weather or for defining threshold limits for the animal to cope with the environment. Moreover, mild infection when associated with high baseline temperature of an animal can have serious adverse events not only causing loss of productivity but also actual loss of life.
Body temperature is a key parameter for monitoring animal physiological, health and welfare status. Animal stressors, such as heat loads, infections, parasites and metabolic diseases, or physiological processes, such as lactation and estrus, can alter body thermoregulation, and knowledge of body temperature variation pattern may help to improve livestock husbandry. For many clinical, pathological, or physiological uses, brain temperature (BrT) seems to be more sensitive to change in the animal status than any core temperature (CrT) in the body. Several studies comparing invasive brain monitoring (BrT) with invasive CrT were performed at different organs or sites of human body. However, little information is available for livestock. In sharp contrast, the ABTT temperature measuring systems of the present disclosure measures brain temperature non-invasively and allows a noninvasive way to assess thermoregulatory responses while serving as an index of hypothalamic temperature, which plays a vital role in regulating feeding intake, endocrine and immunologic functions. However, rectal temperature (RcT) is the most common clinical measure of CrT in cattle because invasive measurement of brain temperature is not possible outside research settings. BrT, carotid arterial blood temperature (CtT), and RcT in conscious sheep exposed to 40° C., 22° C. and 5° C. has been measured. The observed values of RcT were consistently higher than CtT and BrT, for all exposures. Applicant confirmed higher rectal temperature than brain temperature, noting that temperature levels causing brain injury as yet unknown were identified by the inventions of the present disclosure.
The bovine experiments herein disclosed showed that intracranial (ABTT) measurements respond to thermally induced stress more rapidly and to a greater degree than core (Rectal). ABTT not only provided continuous (at 0.75 Hz) monitoring of temperature but also of temperature variations. Adhesive patches and sensors described by the Applicant in previous patent applications were used in the studies.
By identifying herein the thermal and fractal patterns using ABTT temperature monitoring, the present disclosure provides a method, apparatus, and system for Brain Heat Stress Detection, shown in
Once the thermal profile acquired by temperature sensor 8746 starts to depart from a safe thermal profile, or when certain critical levels of brain temperature are identified, the signal is recognized by controller 8748, based on comparison of the received signal with predetermined values for critical temperate values or unsafe thermal patterns stored in non-transitory memory 8750. Controller 8748 is configured to recognize the abnormal signal and then to activate wireless transmitter 8752, which in an exemplary embodiment may be a short-range transmitter. Exemplary transmitters include a Bluetooth, Wi-Fi, cell phone, or radio waves, to transmit the signal to wireless receivers 8758a-c remotely located to inform a farmer about the health of the animals and risk of heat stress. Once an abnormal signal is identified, controller 8748 couples a signal from GPS 8754 in order to identify the location of the animal at risk. Once a signal is transmitted to a remote station 8758a-c, and GPS 8754 informs processor 8748 of location, processor 8748 is configured to execute a program to activate a nearby thermal actuator 8744, exemplified herein as a spray to spray cold water in the area where the animal is located.
Once temperature sensor 8746 measures temperature reaching high risk levels for heat stress exemplified herein by temperature equal to or higher than 38.3° C., controller 8748 is configured to transmit a signal to one or more remote receivers 8758a-c, warning a foreman or farmer. Once temperature sensor 8746 measures temperature reaching critical levels, exemplified herein by temperature equal to or higher than 39.2° C., controller 8748 is configured to transmit a signal to a plurality of remote receivers such as receiver 8758a, warning the owner, receiver 8758b, warning the veterinarian, and receiver 8758c, warning the foreman.
A method using the described apparatus includes the following steps: (1) measuring temperature (preferably at the ABTT site in animals); (2) identifying temperature level and thermal pattern (such as slope of the curve and/or the velocity of temperature increase) every 1 minute or less (or preferably every 30 seconds or less); it should be understood that any frequency of measurement ranging from every 10 minutes to every 1 second is within the scope of the disclosure, but the most frequent measurements possible is preferred; (3) although this next step is optional, controller 8748 may be configured to predict the final thermal pattern based on the slope acquired; in step (4) controller 8748 is configured to compare the acquired slope (or thermal pattern) or temperature level with a predetermined safe thermal pattern or temperature threshold (e.g., 38.3° C. or 39.2° C. stored in non-transitory memory 8750; if in the next step (5) controller 8748 identifies a departure from a safe thermal pattern or temperature level, then in next step (6) controller 8748 acquires a location signal from GPS 8754 and pairs the signal from GPS 8754 with the temperature level signal; and in next step (7) activates wireless transmitter 8752 to transmit a signal package (temperature level plus location) to at least one remote receiver 8758a-c; an optional step (8) includes controller 8748 actuating at least one thermal actuator 8744.
While various embodiments of the disclosure have been shown and described, it is understood that these embodiments are not limited thereto. The embodiments may be changed, modified, and further applied by those skilled in the art. Therefore, these embodiments are not limited to the detail shown and described previously herein, but also include all such changes and modifications. It should also be understood that any part of series of parts of any embodiment can be used in another embodiment, and all of those combinations are within the scope of the disclosure.
This application claims priority from U.S. Provisional Application No. 61/889,561 filed Oct. 11, 2013, and is a continuation-in-part of U.S. patent application Ser. No. 14/479,099 filed Sep. 5, 2014, which is a continuation application of U.S. patent application Ser. No. 13/709,676 filed Dec. 10, 2012, now U.S. Pat. No. 8,834,020, which is a continuation application of U.S. patent application Ser. No. 11/585,344 filed Oct. 24, 2006, now U.S. Pat. No. 8,328,420, which is a complete application of U.S. Provisional Application Nos. 60/729,232 and 60/802,503 filed on Oct. 24, 2005 and May 23, 2006, respectively, and is a continuation-in-part of U.S. patent application Ser. No. 10/786,623, filed Feb. 26, 2004, now U.S. Pat. No. 8,849,379, the entire content of each of which is incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| 61889561 | Oct 2013 | US | |
| 60802503 | May 2006 | US | |
| 60729232 | Oct 2005 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 13709676 | Dec 2012 | US |
| Child | 14479099 | US | |
| Parent | 11585344 | Oct 2006 | US |
| Child | 13709676 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 14479099 | Sep 2014 | US |
| Child | 14512427 | US | |
| Parent | 10786623 | Feb 2004 | US |
| Child | 11585344 | US |
