Patent Application
20100036272
The present invention relates to metabolic measurement system that uses a multi-function airway adapter, which monitors the amounts of oxygen (O2) in the respiration of an individual, as well as the respiratory flow of the amount of one or more of carbon dioxide (CO2), nitrous oxide (N2O), or an anesthetic agent other than nitrous oxide in the respiration of the individual. More specifically, the present invention relates to a metabolic measurement system that uses an integrated airway adapter, which is capable of monitoring, by luminescence quenching techniques, the fractions, or concentrations, of gases, such as O2 in real time or breath-by-breath, as well as monitoring one or both of respiratory flow and, by infrared absorption techniques, the fractions, or concentrations, of gases such as CO2, N2O, and anesthetic agents.
A. Respiratory Gas Monitoring
Various types of sensors that are configured to communicate with the airway of a patient to monitor substances such as gases or vapors in the respiration of the patient are known in the art. Molecular oxygen, carbon dioxide, and anesthetic agents, including nitrous oxide, are among the types of substances that may be detected with known sensors.
Typically, side-stream gas sensors are used during surgical procedures to indicate the condition of a patient to an anesthesiologist. Respiratory gas sensors may also be used in a variety of other medical procedures, such as heart stress tests with an individual on a treadmill, in other tests for monitoring the physical condition of an individual, and the like. Side-stream sampling requires the use of small bore sampling lines to draw gas from the breathing circuit for remote analysis. The problems associated with side-stream gas sampling are well known and include the following:
a) impeding of the sample line by the presence of water and patient secretions;
b) introduction of variable delay which creates synchronization difficulties when combining flow and gas concentration measures;
c) loss of signal fidelity due to low pass filtering; and
h) handling of exhaust, which may contain anesthetic agents, blood, secretions, etc.
The use of mainstream sensors to monitor respiratory and anesthetic gases has the potential to solve the problems associated with side-stream sensors, especially when combining gas and flow and/or pressure signals.
B. Infrared Absorption
Infrared absorption has long been employed to detect and monitor gases, such as CO2, N2O, and other anesthetic agents, in the respiration of a patient. In infrared absorption (IR) techniques, infrared light of one or more wavelengths and of known intensity is directed into a stream of respiratory gases. The wavelength or wavelengths of such radiation are selected based on the gas or gases being analyzed, each of which absorbs one or more specific wavelengths of radiation. The intensity of the radiation which passes through the stream of respiratory gases, which radiation is typically referred to as “attenuated radiation”, is measured and compared with the known intensity of the radiation emitted into the stream. This comparison of intensities provides information about the amount of radiation of each wavelength that is absorbed by each analyzed gas, which, in turn, provides information about the amount (i.e., the concentration or fraction) of that gas in the patient's respiration.
U.S. Pat. No. 4,859,858 (hereinafter “the '858 patent”) and U.S. Pat. No. 4,859,859 (hereinafter “the '859 patent”), both of which issued to Knodle et al. on Aug. 22, 1989, and U.S. Pat. No. 5,153,436 (hereinafter “the '436 patent”), issued to Apperson et al. on Oct. 6, 1992, each disclose apparatus that include infrared absorption type sensors for measuring the amount of one or more specific gases in the respiration of a patient.
Typically, infrared gas sensors, such as those disclosed in the '858, '859, and '436 patents, include a source from which infrared radiation is emitted. The emitted infrared radiation is focused into a beam by a mirror. The beam is transmitted through a sample of the gases being analyzed. After passing through the gases, the infrared radiation beam passes through a filter. The filter reflects all of the radiation except for the radiation in a narrow band which corresponds to a frequency absorbed by the gas of interest. This narrow band of radiation is transmitted to a detector, which produces an electrical output signal proportional in magnitude to the magnitude of the intensity of the infrared radiation impinging upon the detector. As the intensity of the radiation that passes through the filter is attenuated to an extent that is proportional to the concentration of a gas of interest, the strength of the signal generated by the detector is inversely proportional to the concentration of the gas of interest.
Infrared (IR) type gas sensors that are configured to substantially simultaneously measure the amounts of more than one type of gas in the respiration of a patient are also known. One such sensor, disclosed in U.S. Pat. No. 5,296,706 (hereinafter “the '706 patent), issued to Braig et al. on Mar. 22, 1994, includes a plurality of discrete channels for facilitating the independent detection of six or more different anesthetic agents. The article, Burte, E. P. et al., “Microsystems for measurement and dosage of volatile anesthetics and respirative gases in anesthetic equipment”, MEMS 98 Proceedings., The Eleventh Annual International Workshop on Micro Electro Mechanical Systems, Pages 510-514 (1998) (hereinafter “the Burte Article”), discloses, among other things, a mainstream, multichannel sensor apparatus that is configured to simultaneously measure the amounts of a combination of anesthetic gases in the respiration of a patient.
Infrared type gas sensors typically employ a cuvette to sample the respiration of a patient via a nasal cannula or an endotracheal tube and a mechanical ventilator. The cuvette channels respiratory gases to a specific flow path and provides an optical path between an infrared radiation emitter and an infrared radiation detector, both of which can be detachably coupled to the cuvette.
A typical cuvette is molded from a polymer or other appropriate material and has a passage defining the flow path for the gases being monitored. The optical path crosses the flow path of the gases through windows in the sidewalls of the cuvette aligned along opposite sides of the flow passage, allowing the beam of infrared radiation to pass through the cuvette.
The windows are generally formed from sapphire because of sapphire's favorable optical properties. However, sapphire is a relatively expensive material. Consequently, these cuvettes are almost invariably cleaned, sterilized, and reused. The cleaning and sterilization of a cuvette is time consuming and inconvenient; and the reuse of a cuvette may pose a significant risk of contamination, especially if the cuvette was previously used in monitoring a patient suffering from a contagious and/or infectious disease.
Efforts have been made to reduce the cost of cuvettes by replacing the sapphire windows with windows fabricated from a variety of polymers. One of the major problems encountered in replacing sapphire cuvette windows with polymer windows is establishing and maintaining a precise optical path length through the sample being analyzed. This is attributable to such factors as a lack of dimensional stability in the polymeric material, the inability to eliminate wrinkles in the windows, and the lack of a system for retaining the windows at precise locations along the optical path.
Cuvette windows that are formed from polymers, including polypropylene, may limit the types of substances flowing through an airway adapter that may be monitored or measured by use of infrared techniques. This is because polymers typically include hydrocarbons, which may limit the transmissivity of polymers for some infrared and possibly other wavelengths of radiation that may be used to measure the amounts of certain substances.
U.S. Pat. No. 5,693,944 (hereinafter “the '944 patent”), issued to Rich on Dec. 21, 1997, discloses a cuvette, a method for using the same, and a method for manufacturing the same. The cuvette and methods of use disclosed in the '944 patent eliminate the problems that were previously encountered in attempts to use polymers in the place of sapphire windows. The '944 patent discloses fashioning windows from a malleable homopolymer, such as biaxially oriented polypropylene, in the thickness range of 25 μm to 125 μm. The use of this inexpensive polypropylene material allows for the fabrication of single-use, disposable cuvettes.
C. Luminescence Quenching and Fuel Cells
Luminescence quenching and fuel cells are techniques that have been used to measure oxygen concentrations in gases. In use of luminescence quenching to measure oxygen concentrations, a luminescable material is excited to luminescence. Upon exposure of the luminescing material to a gas mixture including oxygen, the luminescence is quenched, depending upon the amount (i.e., concentration or fraction) of oxygen to which the luminescable material is exposed, or the amount of oxygen in the gas mixture. Accordingly, the rate of decrease in the amount of luminescence, or quenching of luminescence, of the luminescable material (i.e., the amount of light emitted by the luminescable material) corresponds to the amount of oxygen in the gas mixture.
Typically, luminescence quenching requires the emission of excitation radiation from a source toward a luminescable material of a luminescence chemistry that may be quenched by, or is specific for, one or more types of gas (e.g., oxygen, carbon dioxide, halothane, etc.) to be measured. The excitation radiation causes the luminescable material to be excited and to emit electromagnetic radiation of a different wavelength than the excitation radiation. The presence of the one or more gases of interest quenches, or reduces, the amount of radiation emitted from the luminescable material. The amount of radiation emitted from the luminescable material is measured by a detector and compared with the amount of radiation emitted from the luminescable material in the absence of one or more quenching gases in order to facilitate a determination of the amount of the one or more sensed, quenching gases in the respiration of a patient.
A typical fuel cell include a gold cathode and a lead anode surrounded by an electrolyte. A membrane protects the cathode and anode. The gas to be monitored diffuses into the cell through the membrane. The oxygen causes an electrochemical reaction in the fuel cell. As a result, the fuel cell generates and electric current in proportion to the partial pressure of the oxygen in the gas. Thus, the amount of current generated by the fuel cell indicates the concentration of oxygen in the gas being analyzed. An example of a mainstream gas monitoring system using a fuel cell is disclosed in U.S. patent application Ser. No. 10/494,273 (publication no. 2004/0267151) the contents of which are incorporated herein by reference.
Luminescence quenching and fuel cells have been used in a variety of applications, including in diagnostic techniques. The use of luminescence quenching or fuel cells in mainstream oxygen sensors has also been disclosed. Nonetheless, these mainstream sensors are not equipped to employ other gas monitoring techniques or to measure respiratory flow, severely limiting the functionality of these luminescence quenching and fuel cell type sensors.
D. Respiratory Flow Monitoring
Respiratory flow measurement during the administration of anesthesia in intensive care environments and in monitoring the physical condition of athletes and other individuals prior to and during the course of training programs and medical tests provides valuable information for assessment of pulmonary function and breathing circuit integrity. Many different technologies have been applied to create a flow meter that meets the requirements of the critical care environment. Among the flow measurement approaches which have been used are:
a) Differential Pressure—measuring the pressure drop or differential across a resistance to flow (flow resistance);
b) Spinning Vane—counting the revolutions of a vane placed in the flow path;
c) Hot Wire Anemometer—measuring the cooling of a heated wire due to airflow passing around the wire;
d) Ultrasonic Doppler—measuring the frequency shift of an ultrasonic beam as it passes through the flowing gas;
e) Vortex Shedding—counting the number of vortices that are shed as the gas flows past a strut placed in the flow stream; and
f) Time of Flight—measuring the arrival time of an impulse of sound or heat created upstream to a sensor placed downstream.
Each of the foregoing approaches has various advantages and disadvantages, and an excellent discussion of most of these aforementioned devices may be found in W. J. Sullivan, G. M. Peters, P. L. Enright, M. D, “Pneumotachographs: Theory and Clinical Application”, Respiratory Care, July 1984, Vol. 29-7, pp. 736-49, and in C. Rader, “Pneumotachography, a Report for the Perkin-Elmer Corporation” presented at the California Society of Cardiopulmonary Technologists Conference, October 1982.
At the present time, the most commonly used device for respiratory flow detection is the differential pressure flow meter. The relationship between flow and the pressure drop across a restriction or other resistance to flow is dependent upon the design of the resistance. Many different resistance configurations have been proposed. The goal of many of these configurations is to achieve a linear relationship between flow and pressure differential.
In some differential pressure flow meters, which are commonly termed “pneumotachs”, the flow restriction has been designed to create a linear relationship between flow and differential pressure. Such designs include the Fleisch pneumotach in which the restriction is comprised of many small tubes or a fine screen to ensure laminar flow and a linear response to flow. Another physical configuration is a flow restriction having an orifice that varies in relation to the flow. This arrangement has the effect of creating a high resistance at low flows and a low resistance at high flows. Among other disadvantages, the Fleisch pneumotach is susceptible to performance impairment from moisture and mucous, and the variable orifice flow meter is subject to material fatigue and manufacturing variabilities.
Most all known prior art differential pressure flow sensors suffer deficiencies when exposed to less than ideal gas flow inlet conditions and, further, possess inherent design problems with respect to their ability to sense differential pressure in a meaningful, accurate, repeatable manner over a substantial dynamic flow range. This is particularly true when the flow sensor is needed to reliably and accurately measure low flow rates, such as the respiratory flow rates of infants.
U.S. Pat. No. 5,379,650 (hereinafter “the '650 patent”), issued to Kofoed et al. on Jan. 10, 1995, has overcome the vast majority of the problems with differential pressure flow sensors with a sensor that includes a tubular housing containing a diametrically oriented, longitudinally extending strut. The strut of the flow sensor disclosed in the '650 patent includes first and second lumens with longitudinally spaced pressure ports that open into respective axially located notches formed at each end of the strut.
Developments in patient monitoring over the past several decades have shown that concurrent measurements of various combinations of exhaled gas flow rate, O2 concentrations, CO2 concentrations, and concentrations of N2O and various other anesthetic agents provide information that is useful in decision making with respect to anesthesia and therapy. By combining flow, airway pressure, CO2, and O2 measurements, one can calculate CO2 elimination (VCO2) and O2 consumption (VO2), which are related to the metabolic status of an individual. Also, these measurements can provide a graphical representation of the expired O2 or CO2 concentration versus expired volume which provides information about gas exchange in different compartments of the lungs.
While integrated adapters that include both flow and infrared CO2 sensors are known, separate apparatus are presently necessary to obtain O2 measurements and measurements of respiratory flow or of CO2 or N2O and other anesthetic agents. The various apparatus that are needed to simultaneously acquire a combination of the respiratory O2 signals, respiratory flow signals, airway pressure signals, and signals representative of amounts of CO2, N2O, or anesthetic agents would require multiple components if such components were all available in a mainstream configuration. Such “stacking” of multiple sensors at the patient's airway is cumbersome and adds undesirable volume (dead space) and resistance to the breathing circuit.
It would be highly desirable to have an airway adapter which combines a luminescence quenching sensor with one or both of an infrared gas sensor and a respiratory flow sensor in a configuration which is convenient to use and which minimizes phase lag and internal dead space of the combination.
The present invention is directed to a metabolic measurement system that includes an integrated airway adapter for monitoring, in real time, breath-by-breath amounts of substances, such as O2, CO2, N2O, and anesthetic agents in the respiration of an individual, which includes normal respiratory gases, as well as other substances that are inhaled and exhaled by the individual. The airway adapter of the present invention is a compact adapter that integrates at least two functions into a single unit that meets the requirements for clinical patient monitoring. The airway adapter may include a combination of different types of substance detection components or a combination of one or more substance detection components and a respiratory flow detection component. From these measurements, metabolic parameters, such as oxygen consumption or oxygen uptake, carbon dioxide production or carbon dioxide elimination, respiratory quotient (RQ), resting energy expenditure (REE), or any combination of such measurements, can be determined.
In an exemplary embodiment of the present invention, the O2 sensing portion of an integrated airway adapter, incorporating teachings of the present invention, includes a fuel cell or a quantity of luminescable material, the luminescence of which is quenched upon exposure to O2, located in communication with a flow path along which respiratory gases are conveyed through the airway adapter so as to be exposed to the respiratory gases. The luminescable material of the O2 sensing portion may be carried by a removable, replaceable portion of the airway adapter to facilitate reuse of the airway adapter. A source of excitation radiation may be configured to be coupled to the airway adapter so as to direct radiation through a window of the airway adapter and toward the luminescable material to excite the same to luminesce, or to emit radiation. The amount of radiation emitted from the excited luminescable material may be measured with a detector, which may also be configured for assembly with the airway adapter, which detects emitted radiation through a window of the airway adapter.
The present invention further contemplates that the integrated airway adapter also includes a flow sensor. In one embodiment, the flow sensor is a pneumotach that includes two pressure ports, which facilitate the generation of a differential pressure across an orifice of the pneumotach. One of the pressure ports may facilitate monitoring of airway pressure. Alternatively, the flow sensor may have more than two ports, with at least one of the ports facilitating measurement of the airway pressure. The respiratory flow sensor preferably has the capability of accommodating a wide variety of gas flow inlet conditions without adding significant system volume or excessive resistance to the flow of respiration through the integrated airway adapter of the present invention. The design of the respiratory flow sensor of the present invention may also substantially inhibit the introduction of liquids into the pressure ports or monitoring system of the sensor.
The flow sensor may include a flow resistance element (whether the strut or the gas concentration monitoring portion) which creates a nonlinear differential pressure signal. To obtain adequate precision at extremely high and low flow rates, a very high resolution (e.g., 18-bit or 20-bit) analog-to-digital (A/D) conversion device may be used. The use of such a very high resolution A/D converter allows a digital processor to compute flow from the measured differential pressure by using a sensor characterizing look-up table. This technique eliminates the need for variable or multiple gain amplifiers and variable offset circuits that might otherwise be required with use of a lower resolution A/D converter (e.g., a 12-bit A/D converter).
Alternatively, or in addition to the flow sensor, an integrated airway adapter incorporating teachings of the present invention may include a gas sensor configured to measure amounts of CO2, N2O, or anesthetic agents in the respiration of an individual. As an example, the airway adapter may include a gas sensor that employs infrared absorption techniques. Such an exemplary gas sensor may include a chamber with a pair of opposed, substantially axially aligned windows flanking a flow path through the airway adapter. The windows preferably have a high transmittance for radiation in at least the intermediate infrared portion of the electromagnetic spectrum. It is essential to the accuracy of the infrared gas sensor that the material used for the windows transmit a usable part of the infrared radiation impinging thereupon. Thus, the window material must have appropriate optical properties. Preferred window materials include, but are not limited to, sapphire and biaxially oriented polypropylene. Substantial axial alignment of the windows allows an infrared radiation beam to travel from a source of infrared radiation, transversely through the chamber and the gas(es) flowing through the chamber, to an infrared radiation detector. Alternatively, the airway adapter may include a single window and a reflective element, such as a mirror or reflective coating. These elements facilitate the direction of infrared radiation into and across the chamber and the reflection of the infrared radiation back across and out of the chamber to a radiation detector. Signals from the detector facilitate determination of the amounts (i.e., concentrations or fractions) of one or more gases, such as CO2, N2O, and anesthetic agents, in respiration flowing through the chamber.
The integrated airway adapter can be either reusable or disposable. If the airway adapter is designed to be disposable, the infrared absorption windows and the windows that facilitate detection of luminescence quenching should be made of an inexpensive material. If the airway adapter is designed to be reused, the windows of the infrared gas sensor may be detachable from the remainder of the airway adapter so as to facilitate the cleaning and sterilization of nondisposable windows. Alternatively, the windows may remain on the airway adapter during cleaning and sterilization thereof. If luminescable material is carried upon any portion of one or both windows, the luminescable material may be removed from the windows during cleaning and subsequently replaced or, if the luminescable material will withstand the cleaning and sterilization processes, the luminescable material may remain on the windows during these processes.
Injection molding processes may be used to manufacture the airway adapter of the present invention. The consistency of product obtainable from the injection molding process provides a high degree of interchangeability, thereby eliminating the need for a calibration procedure to be performed during setup or with a disposable adapter replacement.
In addition, the integrated airway adapter may incorporate a specific instrument connection scheme to facilitate the proper assembly of external components (e.g., an infrared emitter and detector, a luminescence quenching source and detector, etc.) with the airway adapter, as well as to facilitate the proper assembly of the airway adapter with a respiratory airway. For example, but not to limit the scope of the present invention, the airway adapter may include colors, optical coding, or other suitable types of coding to facilitate correct assembly or may be configured so as to prevent improper assembly.
These and other objects, features, and characteristics of the present invention, as well as the methods of operation and functions of the related elements of structure and the combination of parts and economies of manufacture, will become more apparent upon consideration of the following description and the appended claims with reference to the accompanying drawings, all of which form a part of this specification, wherein like reference numerals designate corresponding parts in the various figures. It is to be expressly understood, however, that the drawings are for the purpose of illustration and description only and are not intended as a definition of the limits of the invention. As used in the specification and in the claims, the singular form of “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise.
The illustrated airway adapter 20 is designed for connection with a breathing circuit that communicates with the airway of a patient. Airway adapter 20 may be connected between a patient ventilation device and the tubing of a mechanical ventilator. For example, first tubular portion 24 of airway adapter 20 may be connected to an endotracheal tube inserted in the trachea of a patient, while second tubular portion 26 of airway adapter 20 is attached to the tubing of the mechanical ventilator. Alternatively, airway adapter 20 may be connected to a breathing mask or other apparatus that are less invasive than endotracheal tubes. Airway adapter 20 need not be connected to a mechanical ventilator, but may be connected with a source of respiratory gases (e.g., an oxygen source) or communicate directly with the air from the patient's environment. As shown, first and second tubular portions 24 and 26 have bores of varying diameter and substantially circular cross-sections, with a gas concentration monitoring portion 28 disposed therebetween. Second tubular portion 26 houses a respiratory flow monitoring device 30.
Gas concentration monitoring portion 28 includes a gas sensing portion 230, which is configured to employ luminescence quenching techniques to measure the partial pressure or amount of oxygen or other gases that flow through airway adapter 20. As illustrated in
With specific reference to
Luminescable material 232 may be dispersed throughout passages or openings formed in membrane 236. The passages and openings through membrane 236 may have diameters or widths of about 0.1 μm to about 10 μm, as the diffusion constant for molecular oxygen through membranes of such dimensions is large enough to provide a luminescence quenching response time of sufficiently short duration to facilitate a measurement of the luminescence quenching rate on a breath-by-breath basis, or in real time. Stated another way, these membrane 236 dimensions facilitate the substantially immediate exposure of luminescable material 232 to oxygen and other luminescence quenching substances as these substances flow through or past membrane 236.
If airway adapter 20 is reusable, membrane 236 may be removable from the remainder of airway adapter 20 so as to facilitate replacement thereof with a new membrane 236 carrying luminescable material 232 and, thus, to facilitate accurate determinations of the concentration of oxygen or other gases with subsequent use of airway adapter 20. Alternatively, if luminescable material 232 will withstand the cleaning and sterilization processes to which airway adapter 20 is subjected, membrane 236 may be permanently secured to airway adapter 20 and reused following cleaning and sterilization thereof.
Porphyrins are an example of a material that may be used as luminescable material 232. Porphyrins are stable organic ring structures that often include a metal atom. When the metal atom is platinum or palladium, the phosphorescence decay time ranges from about 10 μs to about 1,000 μs. Porphyrins are also sensitive to molecular oxygen. When porphyrins are used as luminescable material 232, it is preferred that the porphyrins retain substantially all of their photo-excitability with repeated use. Stated another way, it is preferred that the porphyrins be “photostable”. Fluorescent porphyrins, such as meso-tetraphenyl porphines, are particularly photostable. The various types of porphyrins that may be used as luminescable material 232 to facilitate oxygen detection include, without limitation, platinum meso-tetra(pentafluoro)phenyl porphine, platinum meso-tetraphenyl porphine, palladium meso-tetra(pentafluoro)phenyl porphine, and palladium meso-tetraphenyl porphine. Of course, other types of luminescable materials that are known to be quenched upon being exposed to oxygen, carbon dioxide, or another analyzed substance (e.g., gas, liquid, or vapor) may also be used in airway adapters incorporating teachings of the present invention.
Membrane 236 is preferably formed from a material that is compatible with luminescable material 232. Moreover, it is preferred that the material of membrane 236 be compatible with respiratory gases, as well as nontoxic to the patient and, preferably, to the environment.
Materials that may be used to form membrane 236 include, but are not limited to, porous polyvinylchloride (PVC), polypropylene, polycarbonate, polyester, polystyrene, polymethacrylate polymers, and acrylic copolymers. Specifically, microporous polycarbonate filtration membranes available from Pall Gelman Sciences of Ann Arbor, Mich., and from Whatman, Inc. of Clifton, N.J., (track-etched microporous polycarbonate filtration membranes with a thickness of about 10 μm and a pore size of about 0.4 μm) are useful as membrane 236.
As indicated previously herein, it is preferred that membrane 236 be permeable to respiratory gases, including oxygen. As respiratory gases flow past, into, or through membrane 236, the respiratory gases, including oxygen, contact luminescable material 232 carried thereby. The luminescence of, or intensity of radiation emitted from, luminescable material 232 is then quenched to a degree that is based on the amount of oxygen or other luminescence quenching gases in the respiratory gases. The permeability of membrane 236 to respiratory gases also has an effect on the number of luminescable material 232 particles that is exposed to the respiratory gases and may, therefore, affect the amount of luminescence quenching that occurs as luminescable material 232 is exposed to oxygen and other luminescence quenching gases present in the respiratory gases that flow through membrane 236.
Luminescable material 232 may be applied to membrane 236 by known processes. By way of example and not to limit the scope of the present invention, a solvent may be used to introduce luminescable material 232 onto a surface of membrane 236, as well as into openings thereof. Preferably, the solvent does not substantially dissolve the material of membrane 236. The solvent may, however, interact with the material of membrane 236 in a manner that causes membrane 236 and the openings thereof to swell, so as to facilitate the introduction of luminescable material 232 into the openings. Exemplary solvents that may be used to apply luminescable material 232 to membrane 236 include, without limitation, hexane, petroleum ethane, toluene, tetrahydrofuran, methylene chloride, trichloroethylene, xylene, dioxane, isopropyl alcohol, and butanol, as well as mixtures of any of the foregoing. Of course, the use of a particular solvent depends on its compatibility with both luminescable material 232 and with the material of membrane 236. Once luminescable material 232 has been applied to membrane 236, the solvent may be evaporated or otherwise removed from membrane 236 in a manner that leaves luminescable material 232 on the surface and within the openings of membrane 236.
Alternatively, as shown in
With returned reference to
Known processes may be used to apply overcoat layer 242 to membrane 236. For example, a dissolved polymer may be applied to membrane 236 to form overcoat layer 242. Alternatively, a preformed overcoat layer 242 may be adhered to membrane 236 by known means, so long as the overcoated membrane 236 retains the desired properties.
In use of gas sensor 230, membrane 236 thereof is preferably disposed over a thermal source of a known type, such as thermal capacitor 244. Thermal capacitor 244 communicates with a heater component 246 (
One example of the manner in which thermal capacitor 244 and heater component 246 may communicate with each other includes providing a floating, thermally conductive heater component 246 on transducer housing 22 (
Transducer housing 22, as depicted in
Transducer housing 22 also contains at least a portion of a detector 258 positioned to receive radiation emitted from luminescable material 232 and configured to measure an intensity of such emitted radiation. Accordingly, detector 258 is positioned toward window 234 and toward luminescable material 232. Preferably, a filter 259 is disposed between luminescable material 232 and detector 258 so as to prevent wavelengths of electromagnetic radiation other than those emitted from luminescable material 232 from interfering with the luminescence and luminescence quenching measurements obtained with detector 258. Other features and advantages of a luminescence quenching type sensor that may also be employed in the present invention is disclosed in U.S. Pat. No. 6,325,978, issued to Labuda et al. on Dec. 4, 2001, which has been assigned to the same assignee as the present invention.
Gas concentration monitoring portion 28 of airway adapter 20 provides a seat for transducer housing 22. An integral, U-shaped casing element 36 positively locates transducer housing 22 across airway adapter 20 and in the transverse direction indicated by arrow 38 in
Center section 32 may also include an infrared sensor portion 33 with first and second axially aligned windows 40 and 42, respectively (only window 42 is shown in
Cuvette windows 40 and 42 for infrared absorption measurements have typically been fabricated from sapphire because of sapphire's favorable optical properties, stability, and resistance to breakage, scratching, and other forms of damage. Alternatively, the cost of the cuvette can be reduced to the point of making it practical to dispose of the cuvette after a single use by fabricating the cuvette windows from an appropriate polymer. It is essential to the accuracy of the infrared absorption portion of the gas concentration monitor that the polymer transmit a usable part of the infrared radiation impinging upon it. Thus, the window material must have the appropriate optical properties for measuring the desired substances. An exemplary window material exhibiting such properties with respect to measuring an amount of carbon dioxide present in the respiration of a patient is biaxially oriented polypropylene. Other materials may also be used, depending upon the transmissivities thereof for certain wavelengths of radiation that are to be used to detect the presence or amounts of particular substances in the respiration of a patient.
Referring again to
The internal configuration and design of infrared detector 254, which preferably monitors, in real time, the amounts of CO2, N2O, or anesthetic agents in the respiration of an individual is thoroughly discussed in U.S. Pat. No. 5,616,923 (hereinafter “the '923 Patent”). It is understood that infrared CO2 monitor devices such as those disclosed in the '858, '859, and '436 patents, as well as other CO2 detection devices, could be used in transducer housing 22. In addition to one or more infrared sensors, infrared detector 254 may include any combination of other components, including a reference sensor, optics (e.g., lenses, filters, mirrors, beam splitters, etc.), coolers, and the like.
The infrared signals detected by infrared detector 254 can be ratioed to provide a signal accurately and dynamically representing the amount of CO2, N2O, or an anesthetic agent flowing through airway adapter 20.
Airway adapter 20″ includes a window 234 formed through a top portion thereof. Window 234 is transparent to (i.e., has a high transmissivity for) wavelengths of radiation that are used to excite luminescable material 232 on a membrane 236 positioned within flow passage 34 and adjacent to window 234. In addition, window 234 is transparent to one or more wavelengths of radiation that are emitted from luminescable material 232 and quenched by an analyzed substance to a degree that relates to an amount of the analyzed substance in respiration of an individual or in another gas mixture.
In addition, airway adapter 20″ includes windows 40, 42 positioned on opposite sides of flow passage 34. Windows 40 and 42 facilitate the direction of radiation of one or more specified infrared wavelengths across flow passage 34 to facilitate the measurement of amounts of one or more substances, such as carbon dioxide or nitrous oxide or other anesthetic agents, that are present in the respiration of an individual as the individual's respiration passes through a location of flow passage 34 between which windows 40 and 42 are positioned. Accordingly, windows 40 and 42 are each preferably formed from a material that is substantially transparent to (i.e., has a high transmissivity for) infrared wavelengths that are desired for use in measuring amounts of one or more substances in respiration of the individual.
Transducer housing 22″ contains at least a portion of a radiation source 256 positioned to direct one or more wavelengths of radiation that are capable of exciting luminescable material 232 into luminescence through window 234, toward luminescable material 232. Radiation source 256 may include optics (e.g., filters, lenses, beam splitters, etc.) that direct radiation toward the appropriate location and that filter out one or more undesirable wavelengths of the radiation emitted from radiation source 256. In addition, transducer housing 22″ carries a luminescence detector 258, as well as any optics (e.g., filters, lenses, beam splitters, etc.) associated therewith, which are respectively positioned to receive and detect at least one wavelength of radiation that is emitted by luminescable material 232 and that is quenched by exposure to a substance of interest to a degree that indicates an amount of the substance to which luminescable material 232 is exposed.
An infrared emitter 252 and an infrared detector 254 are positioned in opposite legs 22a″, 22b″, respectively, of transducer housing 22″. Infrared emitter 252 is oriented within transducer housing 22″ so as to direct one or more infrared wavelengths of radiation through window 40, across flow passage 34, and through window 42 as transducer housing 22″ is assembled with airway adapter 20″. Infrared detector 254, which is positioned adjacent window 42 when transducer housing 22″ is assembled with airway adapter 20″, is oriented so as to receive and detect the one or more infrared wavelengths of radiation emitted by radiation source 256 that exit airway adapter 20″ through window 42.
Alternatively, or in combination with other airway adapter features disclosed herein, as depicted in
Window 40 may be formed from a material that is substantially transparent to (i.e., has a high transmissivity for) infrared wavelengths that are desired for use in measuring amounts of one or more substances in respiration of the individual.
Optics 41 may include one or more mirrors or reflective coatings, as well as other optical components of known types (e.g., lenses, filters, etc.), to direct a beam of radiation that originated from an infrared emitter 252 within transducer housing 22 and was introduced into flow passage 34 of airway adapter 20 back across flow passage 34, through window 40, and to an infrared detector 254 carried by transducer housing 22, positioned adjacent infrared emitter 252.
As in previously described embodiments, airway adapter 20 is configured to seat a transducer housing 22, which carries infrared emitter 252 and infrared detector 254. Upon assembling transducer housing 22 and airway adapter 20, infrared emitter 252 is oriented such that it is positioned to emit infrared wavelengths of radiation into window 40, at least partially across flow passage 34, toward optics 41. Likewise, upon assembling airway adapter 20 and transducer housing 22, infrared detector 254 is oriented so as to receive infrared wavelengths of radiation that have been redirected by optics 41 back out of window 40.
As one or more infrared wavelengths of radiation pass across at least a portion of flow passage 34 adjacent to window 40 and through the respiration of an individual passing through that portion of flow passage 34, each infrared wavelength may be attenuated, or decreased in intensity, to a degree that correlates to an amount of a corresponding substance present in the individual's respiration.
Other exemplary embodiments of airway adapters incorporating teachings of the present invention are depicted in
Window 140 is substantially transparent to (i.e., has a high transmissivity for) at least one wavelength of radiation that excites luminescable material 232 into luminescence. In addition, window 140 is substantially transparent to one or more of infrared wavelengths of radiation that are useful for measuring amounts of one or more substances present in respiration or other gas mixtures passing through a location of flow passage 34 positioned between windows 140 and 142.
Window 142 is substantially transparent to the one or more infrared wavelengths of radiation to which window 140 is substantially transparent. Window 142 is also substantially transparent to at least one wavelength of radiation that is emitted by luminescable material 232, the intensity of which decreases at a rate that is indicative of an amount of a measured substance in respiration within flow passage 34.
While radiation may pass through any portion of window 140, a membrane 236 carrying luminescable material 232 is positioned adjacent to a portion of window 142. As shown in
A transducer housing 122 configured complementarily to airway adapter 120 includes two legs 122a and 122b, one of which (first leg 122a) is configured to be positioned adjacent to window 140 and the other of which (second leg 122b) is configured to be positioned adjacent to window 142.
First leg 122a of transducer housing 122 carries infrared emitter 252 and radiation source 256, which emits at least one wavelength of radiation that will excite luminescable material 232. Both infrared emitter 252 and radiation source 256 are positioned to emit their respective wavelengths of radiation into window 140 and through flow passage 34. While infrared emitter 252 is also oriented so as to direct radiation emitted therefrom through an unobstructed (by membrane 236) portion of window 142, radiation source 256 is oriented to direct radiation emitted therefrom toward membrane 236 so as to excite luminescable material 232 carried thereby into luminescence.
As an alternative, membrane 236 may substantially cover window 142 if membrane 236 and luminescable material 232 thereon are substantially transparent to one or more wavelengths of infrared radiation that are used to detect the partial pressure or amount of carbon dioxide or one or more other substances present in respiratory or other gases that are flowing through airway adapter 120.
Second leg 122b of transducer housing 122 carries an infrared detector 254 and luminescence detector 258. Infrared detector 254 is positioned to receive and detect one or more infrared wavelengths of radiation exiting airway adapter 120 through window 142. Luminescence detector 258 is oriented to receive and detect one or more wavelengths of radiation that are emitted from luminescable material 232 and that are quenched, or reduced in intensity, to a degree representative of an amount of a monitored substance in respiration to which luminescable material 232 is exposed.
As an alternative to the embodiments illustrated in
Airway adapter 20′ also includes one or more mirrors 41′ that are positioned so as to facilitate measurement of the amounts of one or more of oxygen, carbon dioxide, and anesthetic agents in the respiration of an individual through window 40′. As depicted, airway adapter 20′ includes one mirror 41′, which facilitates collection of measurements that are indicative of an amount of carbon dioxide and/or an anesthetic agent in an individual's respiration. By way of example only, mirror 41′ may be shaped or positioned within flow passage 34 so as to reflect radiation that has been introduced into flow passage 34 through window 40′ and that has traversed at least a portion of the distance across flow passage 34 back through window 40′. Of course, mirror 41′ may actually comprise a group of mirrors or other optical elements (e.g., filters, lenses, etc.) or known types to facilitate the direction of radiation of particular wavelengths to the appropriate locations.
As depicted in
Luminescence detector 258 detects at least one wavelength of radiation emitted from luminescable material 232 that indicates an amount of oxygen present in respiration or another gas mixture flowing through flow passage 34.
Transducer housing 22′, as shown in
Of course, one or more lenses may be associated with radiation source 256′ and/or luminescence detector 258′ to focus radiation being emitted by radiation source 256′ or received by luminescence detector 258′. One or more filters may similarly be associated with radiation source 256′ to limit the wavelengths of radiation to which luminescable material 232 is exposed. Also, one or more filters may be associated with luminescence detector 258′ to restrict the wavelengths of radiation that maybe received thereby.
Referring generally to
When an airway adapter 20, 20′ incorporating teachings of the present invention includes luminescable material 232, the material or materials from which airway adapter 20, 20′ and transducer housing 22, 22′ are formed preferably prevent luminescable material 232 from being exposed to wavelengths of ambient light which may excite luminescable material 232 (i.e., the material or materials are opaque to such wavelengths of radiation). Additionally, the material or materials of airway adapter 20, 20′ and transducer housing 22, 22′ preferably prevent luminescence detector 258 from being exposed to the same wavelengths of ambient radiation that luminescable material 232 emits upon being excited and that are quenched, or reduced in intensity, to a degree that is representative of an amount of oxygen or another analyzed gas or vaporized material to which luminescable material 232 is exposed. One or both of airway adapter 20, 20′ and transducer housing 22, 22′ may also be equipped with light sealing elements or optical filters that further prevent luminescable material 232 and luminescence detector 258 from being exposed to undesirable wavelengths of ambient radiation.
It is also preferred that the material or materials from which airway adapter 20, 20′ and transducer housing 22, 22′ are formed do not emit or fluoresce wavelengths of radiation that would either excite luminescable material 232 or be emitted therefrom upon exposure of airway adapter 20, 22′ or transducer housing 22, 22′ to either ambient radiation or to wavelengths of radiation that are emitted by infrared emitter 252, radiation source 256, or excited luminescable material 232.
Portions of airway adapter 20, 20′ or transducer housing 22, 22′, such as window 40, through which one or more wavelengths of radiation are to be transmitted are preferably formed from materials that do not absorb a substantial amount of the one or more wavelengths of radiation that are to be transmitted therethrough. Stated another way, these portions of airway adapter 20, 20′ or transducer housing 22, 22′ should be relatively transparent to the wavelengths of radiation that are indicative of an amount of one or more particular substances in the respiration of a patient. By way of example only and not to limit the use of polypropylene in airway adapter 20, 20′ or in transducer housing 22, 22′, while polypropylene has a high transmissivity for wavelengths that are used to detect carbon dioxide levels, polypropylene may not have good transmissivity for wavelengths of radiation that may be used to detect levels of other substances.
As discussed above and illustrated in
It is contemplated that the end faces 50 and 52 may be substantially perpendicular to axis A, as shown in
As shown in
Strut 44 also provides a position for pressure ports 62 and 66 and conditions the velocity profile of the flowing gas. Strut 44 is offset from an inner wall 48 of tubular housing 46 and is secured, at both ends, to inner wall 48.
The cross-sectional area of the 44 transverse to a bore axis A should be minimized. The minimization of this dimension is, however, constrained by the diameters of pressure ports 62 and 66. Typically, the cross-sectional area of strut 44 may be about five percent (5%) of the cross-sectional bore area of tubular housing 46 at the location of strut 44.
It should be noted that the diameter of the bore through tubular housing 46, depicted in
Strut 44 further includes notch structures comprising substantially symmetrical first and second notches 58 and 60, both of which are located substantially on axis A of tubular housing 46, notches 58 and 60 extending axially inwardly from first and second end faces 50 and 52, respectively, and laterally through first and second side faces 54 and 56, respectively. A first pressure port 62 of a first lumen 64 opens into first notch 58, and a second pressure port 66 of a second lumen 68 opens into second notch 60. First and second lumens 64 and 68 comprise passages internal to strut 44, which extend into and through first and second male stems 72 and 74, respectively, on an exterior surface of tubular housing 46.
Airway adapter 20 is preferably oriented with first and second male stems 72 and 74 directed upward, such that water condensation and mucus do not clog or otherwise impair pressure ports 62 and 66.
Both pressure ports 62 and 66 face substantially perpendicular to axis A of tubular housing 46, notches 58 and 60 extend axially inwardly to a depth D, at least past pressure ports 62 and 66, and may so extend a distance equal to the height H2 of notches 58 and 60, which, in turn, should be less than or equal to four-tenths ( 4/10) of the height H1 of the strut 44.
Back walls 78 and 80 of notches 58 and 60, respectively, may be arcuate or radiused, as shown in
Floors 82 and 84 and ceilings 86 and 88 of notches 58 and 60, respectively, are preferably substantially planar, or flat, as shown in
Back walls 78 and 80 of notches 58 and 60, respectively, together with restrictions (ridges or lands) 90 comprise a flow obstruction 76 and/or perturbation to the gas flow through flow monitoring device 30, which generates the differential pressure signal measured at first and second pressure ports 62 and 66. The measured differential pressure signal is from either pressure loss or from vena contracta, the contraction of the velocity profile of flowing gases, which is caused by flow obstruction 76. The differential pressure generated from the vena contracta can be modeled by standard fluid mechanics equations such as Euler's or Bernoulli's equation. The differential pressure signal generated from vena contracta is considered “lossless”, meaning that the pressure is restored as the velocity profile is returned to the incident velocity profile.
Respiratory flow, as measured by flow monitoring device 30, is proportional to the square root of the differential pressure, as measured at pressure ports 62 and 66.
Flow obstruction 76 may be varied in a number of ways to yield a different magnitude of measured differential pressure for a given flow rate. First, the cross-sectional area of restrictions (ridges or lands) 90 may be increased or decreased in the plane perpendicular to axis A. Also, the distance from the center of first pressure port 62 to back wall 78 of notch 58 and, likewise, the distance from the center of the second pressure port 66 to back wall 80 of notch 60, may be varied to change the flow response characteristics. The magnitude of the differential pressure signal for a given flow rate can be further increased by reducing the cross-sectional bore area by necking down the inner wall 48 of tubular housing 46.
The length and width of strut 44 may be altered, as desired, to change flow characteristics. These flow characteristics include flow conditioning, signal strength, and signal stability. Ideally, the incident velocity profile to flow obstruction 76 should be the same regardless of the velocity profile incident to airway adapter 20. Signal stability may be compromised when unstable, multidimensional vortex formations are generated by flow obstruction 76. Strut 44 with notch means provides flow conditioning that yields some immunity to inlet velocity profile and yields a stable differential pressure signal in response to the gas flow.
Flow monitoring device 30 may be selectively modified to adapt to the conditions under which flow monitoring device 30 is to operate. In particular, the modification of the cross-sectional flow area in the vicinity of strut 44 may be employed to adjust the dynamic range of the respiratory flow monitoring device 30, as may modifications to the configurations of end faces 50 and 52 and back walls 78 and 80 of notches 58 and 60, and to the lines of transition between notches 58 and 60 and end faces 50 and 52 and side faces 54 and 56. It is preferred to use laterally extending, transversely oriented center (strut 44) restrictions (ridges or lands) 90 and a gradual inner wall transition in the strut area axial length to add symmetry to the flow pattern, normalize the flow, provide immunity to moisture, and provide better repeatability of readings. The notch height H2 or the length of strut 44 may be increased or decreased to accommodate a wider range of inlet conditions, such as might result from employment of flow monitoring device 30 with a variety of endotracheal tubes.
As shown, airway adapter 100 is designed for connection between a patient ventilation device, such as an endotracheal tube inserted into a patient's trachea, attached to a first tubular portion 104 of airway adapter 100, and the tubing of a mechanical ventilator, attached at second tubular portion 106 of airway adapter 100. First and second tubular portions 104 and 106 have bores of varying diameter and of substantially circular cross-section. As shown in
Gas concentration monitoring portion 108 of airway adapter 100 provides a seat for a transducer housing (not shown), similar to transducer housing 22 shown in
As illustrated, airway adapter 100 includes an annular recess 141 formed in first tubular portion 104. Annular recess 141 accommodates a male connecting tube element, shown in broken lines and designated as M1, on the left-hand side of first portion 104 of airway adapter 100. Second tubular portion 106 similarly includes a receptacle 143 configured to accommodate a second male connecting tube element M2, as shown in broken lines, which snaps into receptacle 143 by engaging a stepped slot 145 thereof. Elements M1 and M2 each include a bore of like diameter to the corresponding tubular chambers 130 and 124 of airway adapter 100. Elements M1 and M2 facilitate communication between airway adapter 100 and the airway of an individual and, if necessary, a respirator or other ventilation device.
Gas concentration monitoring portion 108 includes a luminescent sensing window 234 formed through U-shaped casing element 112. Window 234 facilitates the emission of excitation radiation from a source of excitation radiation within a transducer housing assembled with airway adapter 100, into airway adapter 100, and toward luminescable material (e.g., luminescable material 232 shown in
Gas concentration monitoring portion 108 also includes a first axially aligned window 116 and a second axially aligned window 118 (shown in
Airway adapter 100 includes a respiratory flow monitoring device 110, which partially resides in first tubular portion 104, partially resides in second tubular portion 106, and partially resides in gas concentration monitoring portion 108.
Respiratory flow monitoring device 110, which is most clearly depicted in
The heat generated by the radiation sources 252, 256 of transducer housing 22 (
It has been found that this embodiment has many advantages, such as minimization of dead space and moldability in one piece.
Airway adapter 200 is designed for connection between a patient ventilation device, such as an endotracheal tube inserted in a patient's trachea, attached to the first tubular portion 104, and the tubing of a mechanical ventilator, attached to second tubular portion 106. First and second tubular portions 104 and 106 have bores of varying diameter and of substantially circular cross-section, with gas concentration monitoring portion 108 positioned therebetween.
Gas concentration monitoring portion 108 of airway adapter 200 provides a seat for a transducer housing (not shown), similar to transducer housing 22 shown in
In this embodiment, as with the embodiment of
Gas concentration monitoring portion 108 includes a luminescent sensing window 234 formed through U-shaped casing element 112. Window 234 facilitates the emission of excitation radiation from a source of excitation radiation within a transducer housing assembled with airway adapter 200, into airway adapter 200 toward luminescable material (e.g., luminescable material 232 shown in
Gas concentration monitoring portion 108 also includes a first axially aligned window 116 and a second axially aligned window 118 to facilitate the transmittance of an infrared radiation beam from an infrared radiation emitter in the transducer housing, transversely through sampling chamber 114 in airway adapter 200 so that amounts of gases, such as CO2, N2O, and anesthetic agents in the respiration of an individual may be monitored as discussed previously herein.
Airway adapter 200 includes a respiratory flow monitoring device 110, which partially resides in first tubular portion 104, partially resides in second tubular portion 106, and partially resides in gas concentration monitoring portion 108. Respiratory flow monitoring device 110 includes a first pressure port 120 of a first lumen 122 that extends through a first strut 202 and opens into a first tubular chamber 124 of first tubular portion 104. First strut 202 has a tapered portion 204 directed toward first tubular portion 104 to minimize potential flow disturbances. Respiratory flow monitoring device 110 also includes a second pressure port 126 of a second lumen 128 that extends through a second strut 206 and opens into second tubular chamber 130. Second strut 206 has a tapered portion 208 directed toward second tubular portion 106 to minimize potential flow disturbances. Lumens 122 and 128 extend respectively to first and second recesses 132, 134.
Recesses 132 and 134 are configured to minimize dead space and to accommodate male connecting tubes, shown in broken lines and designated as T1 and T2. Recesses 132 and 134 may have internal ribs 210 to securely grip tubes T1 and T2. Tubes T1 and T2 are connected to a flow monitor (not shown), which determines flow rate through a pressure differential detected between pressure ports 120 and 126. This pressure differential is produced through the use of a first annular port 212 and a second annular port 214 at the longitudinal ends of gas sampling chamber 114. First annular port 212 is formed by a first restriction member 216 extending from first strut 202 and blocking a portion of first tubular chamber 124 of first tubular portion 104. The face surfaces 220, 222 of first restriction member 216 are preferably substantially perpendicular to the flow of the respiratory gas through airway adapter 200. Second annular port 214 is formed by a second restriction member 218 extending from second strut 206 and blocking a portion of second tubular chamber 130 of second tubular portion 106. Face surfaces 224, 226 of second restriction member 218 are preferably substantially perpendicular to the flow of the respiratory gas through the airway adapter 200. First restriction member 216 and second restriction member 218 can be any shape, such a circular, oval, rectangular, or the like. However, the preferred shape is a planar disk.
The heat generated by the radiation sources 252, 256 of transducer housing 22 (
One of the uses of the multiple function airway adapter of the present invention is in a metabolic measurement system, which is a system that is capable of providing metabolic measurements, such as oxygen consumption or oxygen uptake, carbon dioxide production or carbon dioxide elimination, respiratory quotient (RQ), resting energy expenditure (REE), or any combination of such measurements. It should be noted that “oxygen update” and “oxygen consumption” are used synonymously, and are both represented by the expression “{dot over (V)}O
Oxygen consumption is a measure of the amount of oxygen that the body uses in a given period of time, such as one minute. It is typically expressed as milliliters of oxygen used per minute (ml/min) or as milliliters of oxygen used per kilogram of body weight per minute (ml/kg/min). Measuring the rate of oxygen consumption is valuable, for example, in anesthesia and intensive care situations because it provides an indication of the sufficiency of a patient's cardiac and pulmonary function. VO2 can also be used to monitor the fitness of an individual or athlete.
Sensor head 22 is removably attached to airway adapter 20 as indicated by arrow A. The sensor head, as in the previous embodiment and described above, includes an infrared sensing system adapted to transmit or receive infrared radiation through the window or pair of windows, and a luminescence quenching system. The luminescence quenching system, as also described above, transmits excitation radiation through an opening, receives emitted radiation from a luminescence material through the same opening or a different opening. Detectors associated with the infrared sensing system and the luminescence quenching system provide signals indicative of a concentration of a gas in the gas flow through the airway adapter. In the embodiment illustrated in
Gas monitoring module 304 includes one or more processors that monitor or determine the concentration of a gas based on the signals from the detectors in the infrared sensing system and the luminescence quenching system. For example, the amount of carbon dioxide can be determined based on the signal from the infrared sensing system, and the amount of oxygen can be determined in gas monitoring module 304 based on the output of the luminescence quenching system. The CO2 and/or O2 levels can be output, for example, as waveforms or a numerical values. Monitoring module also provides signals to the radiation emitters in the infrared sensing system and the luminescence quenching system.
While a hardwire communication link 306 is shown, the present invention contemplates providing a wireless communication link between the portions of the infrared sensing system and the luminescence quenching system located in sensor head 22 and the processing elements located in gas monitoring module 304. In which case, power for the infrared sensing system and the luminescence quenching system can be provided via a power source, such as a battery contained in the sensor head, or via a power cable.
In addition, the present invention contemplates locating the processing elements that act on the signals produced by the detectors to determine the gas concentrations directly in the sensor head. An example of such a system is disclosed in U.S. patent no. 6,954,702, and in U.S. patent applications Ser. No. 11/165,670 (publication no. US-2006-0009707-A1) and Ser. No. 11/368,832 (publication no. US-2006-0145078-A1) the contents of which are incorporated herein by reference. Thus, the signals provided by the sensor head would be the processed signals indicative of the gas concentrations, rather than raw signals produced by the detectors in the gas concentration monitoring systems.
Metabolic measurement system 300 also includes a flow measurement system, generally indicated at 310, that measures the flow of gas through airway adapter 20. In the illustrated embodiment, the flow measurement system measures flow by monitoring a pressure differential that is created across a flow restrictor disposed in the airway adapter. A pair of tubes 312 communicate each side of the flow restrictor to a pressure sensor (not shown), which, in the illustrated embodiment, is located in a flow processing module 314. A pair of ports or terminals 313 are provided that coupled to tubes 312 to communicate the pressure one each side of the flow restrictor with the pressure sensor or sensors in the flow processing module. The flow processing module includes processing elements that enables the rate of flow, or any other related parameter, or waveform thereof, to be determined based on the pressure monitored by the pressure sensor or sensor located in that module. The present invention contemplates that an optional input/output element 316 is provided on gas monitoring module 304 and/or flow monitoring module 314.
The output(s) of gas monitoring module 304 and flow monitoring module 314 are provided to a metabolic parameter processing module 320. More specifically, a processor in the metabolic parameter processing module receive signals from the infrared sensing system, the luminescence quenching system, and the flow measurement system either directly or via the gas monitoring module and the flow monitoring module 314. The processing in the metabolic parameter processing module uses these outputs to determine a metabolic parameter associate with the patient being monitored, such as VO2, VCO2, RQ, REE, or any other metabolic parameters or combinations thereof. The metabolic parameters can be displayed on an input/output device 322 provided on the metabolic parameter processing module. However, the present invention also contemplated providing a separate monitor or display 324 on which the output of gas monitoring module 304, flow monitoring module 314, and/or metabolic parameter processing module 320 are shown or otherwise provided.
In the illustrated embodiment, a hardwire link 326 is shown between metabolic parameter processing module 320 and monitor 324. It is to be understood, however, that this link can also be wireless. Moreover, other links, in place of or in addition to link 326, can be provided between monitor 324 and gas monitoring module 304 and/or flow monitoring module 314.
In an exemplary embodiment of the present invention, gas monitoring module 304, flow monitoring module 314, and metabolic parameter processing module 320 are configured such that each module is capable of physically joining another module and in so joining, creating a communication and/or power link between joined modules. This type of modularity provides a very flexible system for the end user.
Suppose for example, that a user wants to monitor only the flow for that patient. In which case, airway adapter 20 can be provided and coupled to only the flow monitoring module. Monitor 324 can be coupled to the flow monitoring module to display the flow waveform. If the user then decided to monitor the patient's CO2, the gas monitoring module 304 can be provided. It can be linked to the flow monitoring module, if desired, or left separate from the flow monitoring module. The output of the gas monitoring module can also be displayed on the monitor. Finally, if the user decides to also monitor the patient's VO2, the metabolic parameter processing module is added. Again, the metabolic parameter processing module can be separated from or linked with the gas and/or flow monitoring modules. However, the outputs of the gas and flow monitoring module must be provided to the metabolic parameter processing module, because, in this embodiment, it does not contain the processing elements necessary for interpreting the signals from the detectors in the gas and flow monitoring systems.
The present invention also contemplates providing other input/output capabilities for gas monitoring module 304, flow monitoring module 314, and metabolic parameter processing module 320. For example, each or all of these modules can includes displays or other visual or audio indicators to provide information to a user. Input devices, such has keypads, touch screens, buttons, switches, knobs, etc. can be provided for entering information into each module. Also, one or more communication links or terminals and other functionality can be provided for communicating a module with a remote location, either via a hardwire or wirelessly.
If less flexibility is desired, the functionality of the gas monitoring module 304, flow monitoring module 314, and metabolic parameter processing module 320 can be combined into a single housing, effectively combining these three modules.
In the embodiment shown in
As shown, for example, in
In one embodiment, the processing element that communicates with the pressure sensor or sensors to determine the flow rate based on the output of the pressure sensor(s) is also provided in sensor head 334. In addition, a communication link 336 is provided to couple the output of the sensor head to a combined gas/flow sensing module 338. In an alternative embodiment, the processing element for producing the actual flow measurement based on the output of the pressure sensor(s) is located in gas/flow sensing module 338. The present invention also contemplates providing the processor or processors, which use the outputs of the IR sensing system and the luminescence quenching system and provide a meaningful or actual gas constituent measurements, in sensor head 334, gas/flow sensing module 338, or interspersed between these elements. It should be noted that if all of the signal processing is accomplished in sensor head 334, the final outputs can be provided directly to metabolic parameter processing module 320, thereby eliminating the need for gas/flow sensing module 338.
Carrying this concept one step further, the present invention also contemplates providing the metabolic parameter processing elements in sensor head 334. Thus, the entire metabolic measurement system need only include airway adapter 20 and sensor head 334, as shown, for example, in
While a luminescence quenching system has been described, in detail, herein for sensing oxygen, the present invention also contemplates using other oxygen sensing systems in airway adapter 22, sensor head 22, 334, or both. For example, the known electrochemical techniques (e.g. fuel cell) for sensing oxygen can be used in addition to or in place of the luminescence quenching system.
The present invention also contemplates using any form of flow sensing technique to detect the rate of flow of gas through the airway adapter, including those discussed in the Background of the Invention Section of the present invention. To emphasize this point,
A still further airway adapter that is capable of gas constituent and gas flow measurements suitable for use in the present invention is disclosed in U.S. provisional patent application No. 60/808,312, (“the '312 application”) filed May 25, 2006, the contents of which are incorporated herein by reference. The airway adapter disclosed in the '312 application includes a housing having a flow restriction disposed in the flow path between first and second pressure ports. A pressure transducer in the form of an optical interferometer is associated with the pressure ports or the gas flow path between the pressure ports to provide the gas flow measurement. The gas constituent measurements are provided by a IR gas sensing system and/or a luminescence gas sensing system, or any other type of gas constituent sensing system disposed in the airway adapter.
By combining multiple different types of gas constituent and gas flow measurements in to a common housing, module, or sensing head, the present invention enables these measurements to be easily synchronized and used, in conjunction, to make metabolic measurements in real time. The modularity of the components provides flexibility in how the system is implemented and upgraded, while avoiding the need to have on hand more monitoring capability that is actually needed.
The airway adapter shown in
Although the invention has been described in detail for the purpose of illustration based on what is currently considered to be the most practical and preferred embodiments, it is to be understood that such detail is solely for that purpose and that the invention is not limited to the disclosed embodiments, but, on the contrary, is intended to cover modifications and equivalent arrangements that are within the spirit and scope of the appended claims. For example, it is to be understood that the present invention contemplates that, to the extent possible, one or more features of any embodiment can be combined with one or more features of any other embodiment.
Under the provisions of 35 U.S.C. §120/365 this application is a continuation-in-part of U.S. patent application Ser. No. 11/701,187, filed Feb. 1, 2007, which is a continuation-in-part of U.S. patent application Ser. No. 09/841,451, filed on Apr. 24, 2001, currently pending, which is a continuation-in-part of the following: (a) U.S. patent application Ser. No. 09/092,260, filed on Jun. 5, 1998, now U.S. Pat. No. 6,312,389, which is continuation of U.S. patent application Ser. No. 08/680,492, filed on Jul. 15, 1996, now U.S. Pat. No. 5,789,660; (b) U.S. patent application Ser. No. 09/128,897, filed on Aug. 4, 1998, now U.S. Pat. No. 6,815,211; and (c) U.S. patent application Ser. No. 09/128,918, filed on Aug. 4, 1998, now U.S. Pat. No. 6,325,978.
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/US08/52690 | 1/31/2008 | WO | 00 | 7/23/2009 |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 08680492 | Jul 1996 | US |
| Child | 09092260 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 11701187 | Feb 2007 | US |
| Child | 12524321 | US | |
| Parent | 09841451 | Apr 2001 | US |
| Child | 11701187 | US | |
| Parent | 09092260 | Jun 1998 | US |
| Child | 09841451 | US | |
| Parent | 09128897 | Aug 1998 | US |
| Child | 09841451 | US | |
| Parent | 09128918 | Aug 1998 | US |
| Child | 09128897 | US |
