Patent Application
20230110218
Various embodiments relate to the field of healthcare devices and, more particularly, to the fields of liquid spray and atomization of inhaled liquids, finding utility in humidification and misting of aerosols and dispensing of medical treatments by route of inhalation.
Many civilizations, ethnic groups, and regional inhabitants, including the Romans, Germans, Japanese, Turks, and Swedes, have long recognized the healthy properties of elevated humidity provided by communal hot baths, hot springs, and steam saunas. It is also a well-known fact, since at least the time of Hippocrates 2,400 years ago, that infectious diseases occur seasonally. Different diseases occur at completely different times of the year. Those caused by respiratory viruses, like the seasonal flu, respiratory synclinal virus, or the Severe Acute Respiratory Syndrome (SARS) viruses, are strongly correlated with seasons of low absolute humidity, particularly the dry air of the winter months (J. Cohen, Science, 36, 1294-1297, 2020 and J. Shaman, E Goldstein, & M. Lipsitch, Amer. J. Epidem. 173, 127-135, 2011.)
The mechanisms for increased transmission of respiratory viruses in dry environments are incompletely understood, but it is recognized generally that dehydration leaves the respiratory airways more susceptible to infectious agents, particularly to viral infectious agents, such as the flu or the SARS viruses. For example, certain genetic traits, such as those occurring in cystic fibrosis, result in depletion in the volume of airway surface liquid (ASL) that bathes the surface of epithelial cells that line the respiratory tract. The reduction in ASL volume results in an increase in viscosity that impairs mucus clearance from the lungs that leads to chronic airway infections.
Humidistat and humidifier devices help to maintain the humidity in heated buildings. Providing optimal and consistent humidity, however, remains a substantial problem in many human environments, particularly in refrigerated or air-conditioned buildings. The problems are most acute in cold-room or freezer workplaces that render the air in those environments very dry. Facilities such as cold storage or meat-packing plants, where workers are in close proximity, frequently are focal points for the transmission of respiratory infections. At present, there are no convenient or practical means for such workers to maintain optimal hydration of their respiratory tracts while working in such dry environments.
Similarly, airline passengers and crew are exposed to very dry air over many hours particularly during long transcontinental or international flights. The relative humidity levels within airline cabins, while in flight, generally are quite low because of the very cold air present at normal flight altitudes (e.g., more than 30,000 feet above sea level). This extremely dry air is compressed and used to provide fresh air within airline cabins during normal airline flights. The low humidity generally leads to an unhealthy condition within airplane cabins that similarly is conducive to the spread of respiratory diseases.
Increasing the humidity of entire airplane cabins would improve the respiratory health of passengers and crew and likely would decrease the spreading of respiratory bacterial and viral infections. A substantial fraction of water vapor, added to airline cabins, however, would condense on the cold, peripheral structural elements of the airplane cabin causing shorting and corrosion problems with wiring, as well as increasing structural corrosion.
Therefore, despite a great need, there are no practical or convenient means within the prior art for providing optimal humidity to those individuals that need to maintain their mobility while situated in cold or dry environments. Particularly needed is a practical and convenient way to introduce sustained humidity to the upper respiratory tract, including the nasal passages, nasal sinuses, nasopharynx, and pharynx. These are the portions of the upper respiratory tract are the first targets of a respiratory virus entering the respiratory airway, and thus their maintenance is critical to prevention of respiratory infections.
Small, hand-held inhaler devices filled with an aqueous liquid are widely available and could be carried into workplaces and aboard airplanes, trains, cars, and the like. Such inhalers, however, require the user continually to coordinate hand-pump compressions with the inhalation phase (also referred to as the “inhalation segment”) of the breathing cycle (also referred to as the “respiratory cycle”) during use. Because inhaler operation consumes the sustained attention of the user, it is impractical and inconvenient to perform over extended periods of time. Also, inhalers supply humidity solely through the mouth. Inhalers do not supply adequate humidity to the nasal passages and the other outermost regions of the upper respiratory tract that are critical sites for respiratory infections.
External nebulizer devices also can be used to generate aerosols that can be pumped into the nasal passages. Motor-driven fans and pumps commonly are used to drive the aerosols through tubing that connects such external nebulizer devices to the respiratory tracts of users. The aerosols may be delivered into the mouth, or into the nose by employing a nasal mask that is usually formed from solid plastic material with venting holes for exhaust. Such external nebulizer devices generally have large external reservoirs, compressors, pumps, and connecting tubing, however, and therefore are cumbersome and inconvenient to use while working or travelling (e.g., in an airplane). Also, the solid masks of such nebulizer devices generally are uncomfortable to use for extended periods of time.
Small, hand-held, external nebulizer devices that do not have connecting tubing are also available to use for humidification of the environment. However, such hand-held nebulizer devices either require an external supporting structure or need to be held continuously by the user. Such hand-held nebulizer devices also have the disadvantage that the stream of dispensed droplets is not well defined. Consequently, a large excess of droplets must be dispensed because only a small fraction actually enters the nasal passages of the immediate user. Moreover, the inefficient use of liquid in hand-held nebulizer devices causes them to run dry after a few minutes of use, requiring frequent re-filling. These hand-held nebulizer devices also require frequent battery-recharging (because of high, uncontrolled, liquid dispense rates) during continuous use, making them inconvenient to use for extended periods of time. Also, the excess of dispensed droplets has a significant effect on the local environment of the users. For example, neighboring passengers in enclosed spaces (e.g., within airline cabins) may be subjected to the overflow of dispensed droplets, and this can be problematic.
Several chronic disease states also are induced or heightened by lack of humidity in the environment in the upper respiratory tract. One example of such a chronic disease state is inherited cystic fibrosis that results in depletion of the ASL volume and increases mucus viscosity. Periodic treatments for cystic fibrosis, such as hypertonic solutions delivered by inhalers or nebulizers, are beneficial for increasing ASL volume and decreasing mucus viscosity. Without continuous attachment to such an inhaler or nebulizer device, however, there are no convenient means to deliver supplemental liquids to the respiratory airways of cystic fibrosis subjects continuously over longer periods of time (e.g., several hours). Despite a great need, no practical or convenient means exist for providing optimal respiratory humidity to those with chronic diseases that desire free mobility during extended treatment periods.
Embodiments are illustrated by way of example and not limitation in the drawings. While the drawings depict various embodiments for the purpose of illustration, those skilled in the art will recognize that alternative embodiments may be employed without departing from the principles of the technology. Accordingly, while specific embodiments are shown in the drawings, the technology is amenable to various modifications.
The present disclosure concerns various embodiments of a face mask system comprised of an automated liquid-droplet dispenser mechanism (ADM) that can be integrated together with an enclosure to function as “smart humidifier” that can be worn and supported entirely by the head and neck of the user (also referred to as the “wearer” of the face mask system). The face mask system conveniently provides for continuous humidification where mobility of the user is of paramount importance. The ADM additionally serves to minimize water vapor exhaled by the user of the face mask system so that environmental effects are reduced. The technology described herein provides a practical solution to the problem of humidification of the upper respiratory airways for individuals situated in dry environments, like airline passengers and crew, and for other individuals needing a practical way to increase the humidity of the ambient environment.
As further discussed below, the “smart humidifier” can be comprised of a group of elements that cooperate to perform the needed humidifier functions when combined into a self-contained face mask system that may be lightweight (e.g., less than 100 grams in total), and therefore can be supported comfortably by the head and neck of the user. The ADM at the core of the face mask system can controllably increase the humidity of air that is drawn into the nostrils or mouth as the user inhales air from the face mask system. The ADM includes (i) a liquid reservoir (or simply “reservoir”) that may be, for example, a detachable and replaceable cartridge assembly in which liquid is stored, (ii) a droplet generator that is in fluid communication with the reservoir, (iii) a respiratory cycle detector that monitors the “respiratory cycle” or “breathing cycle” of the user, (iv) an electronic timer and controller device (or simply “controller”) that is in electronic communication with the respiratory cycle detector and the droplet generator, (v) a user-interactive timer and controller switch and adjustment device, (vi) an internal power source such as a rechargeable battery, or any combination thereof. All components of the ADM can be contained within, or on the surface of, a face mask enclosure that, during operation, is worn and supported entirely by the head and neck of the user.
The ADM of the present disclosure provides for dispensing, from a self-contained reservoir of liquid, either (i) a short pulse of multiple droplets that are ejected simultaneously or (ii) a sequence of individual droplets that are ejected one at a time. The onset of each dispensing pulse or sequence may begin at a predetermined time point with respect to phases of the user's respiratory cycle, principally the time at which exhalation stops and inhalation begins. Said another way, liquid may be dispensed from the reservoir when the exhalation phase of the breathing cycle ends and when the inhalation phase of the breathing cycle begins. In various embodiments either the rate of droplet dispensing or the duration of the dispensing pulse or sequence (i.e., the dispense period) can be adjusted, for example, based on a characteristic of the user (e.g., desired humidity, average length of inhalation phase, etc.), but may be within predetermined upper and lower bounds to provide adequate humidity to maintain the airway surface liquid (ASL) volume and viscosity—especially of the upper respiratory tract—without providing excess moisture. Thereby, the ADM provides for hydration of the ASL of the upper respiratory tract of the user, while also conserving the total amount of liquid consumed from the reservoir. In this way both the volume and the weight of the reservoir can be minimized to allow for integration of the ADM into, or onto the surface of, the protective face mask enclosure, while still providing for several hours of the droplet dispensing. The self-contained face mask system, comprising the ADM and other elements as further discussed below, thereby provides a convenient and practical solution to the humidification problem that plagues individuals that desire to increase humidification of their respiratory airways, while also desiring to maintain relatively unconstrained mobility and freedom to perform other tasks.
In a preferred embodiment, the enclosure of the self-contained face mask system, when worn, will conform to the face of the user to form a primary cavity between the enclosure and the nose and mouth of the user. The primary cavity accommodates one or more components of the ADM and supports their function. In a further preferred embodiment, the enclosure can be comprised of one or more layers of breathable, protective fabric that are adapted to conform flexibly to the face of the user when worn to form the primary cavity. Advantageously, the breathable, protective fabric may form an enclosure that meets the protective face mask requirements of airlines, airports, workplaces, schools, and the like for minimizing the dissemination of respiratory particles in such facilities. Accordingly, the face mask system of the present disclosure can provide the humidity needed for protection of the respiratory airway epithelial cells that are targets of pathogenic bacteria and viruses, while at the same time can reduce the spread of respiratory bacteria and viruses from person to person.
As mentioned above, the ADM within the protective face mask enclosure can include a reservoir in which liquid is stored prior to dispersal as droplets into a primary cavity that is formed between the face mask enclosure of the system and the nose and mouth of the user. The liquid may be pure water, or the liquid may be an aqueous solution of protective electrolyte substances. Liquid may be supplied together with a refillable cartridge assembly that is detachably connectable to and from the self-contained face mask system, or the liquid may be supplied as a reservoir-refilling kit. In embodiments where the reservoir is designed to be refilled periodically with liquid, the reservoir may be attached fixedly to the enclosure of the self-contained face mask system.
The face mask system of the present disclosure may find utility in settings other than in dry workplace environments or within airline cabins, by providing humidity, electrolytes, and other medications that are advantageous for treating chronic respiratory conditions currently without convenient means to supply such substances to the respiratory tract over extended periods of time, including several hours of use.
For the purpose of illustration, embodiments of the ADM contained within the face mask system may be described in the context of instructions that are executable by a controller, which may be a microcontroller, microprocessor, or some other form of central processing unit (also referred to as a “processor”). For example, executable instructions for controlled dispensation of liquid in the form of droplets may be stored, either as firmware or software, in a memory of the controller and when executed by the controller the instructions may cause the controller to (i) examine measurements generated by a sensor that are indicative of a characteristic of air exhaled through the nostrils or mouth by a user, (ii) generate a signal in response to determining, in real time based on analysis of the measurements, that an exhalation phase has ended, and (iii) transmit the signal to a droplet generator so as to commence a dispensation operation in which liquid droplets are dispensed generally toward the nostrils of the user. Thereafter, the controller may generate a second signal in response to determining, in real time based on analysis of the measurements, that peak inhalation has been achieved. The controller may transmit the second signal to the droplet generator so as to conclude the dispensation operation. Alternatively, the controller may transmit the second signal to the droplet generator after a predetermined amount of time has elapsed as further discussed below. Those skilled in the art will recognize that aspects of the technology could be implemented via discrete logic components (e.g., transistor logic circuits) instead of, or in addition to, firmware or software stored in memory. The principal advantages of storing instructions in a memory (e.g., in the form of firmware or software) can be the convenience and ease at which the instructions can be updated or modified. Particularly advantageous may be operations of an associated processor that modify the stored instructions, or accumulated data, in real time, so as to minimize input noise from environmental sensors comprising the ADM or otherwise improve the droplet-dispensing characteristics of the face mask system.
Brief definitions of terms, abbreviations, and phrases used throughout the present disclosure are given below.
The terms “connected,” “coupled,” and variants thereof are intended to include any connection or coupling between two or more elements, either direct or indirect. The connection or coupling can be physical, logical, or a combination thereof. For example, elements may be electrically or communicatively connected to one another despite not sharing a physical connection.
The terms “electronic timer and controller mechanism,” “timer and controller,” and “controller” broadly refer to components implemented via software, firmware, or hardware that are operable to control elements of the self-contained system. Examples of “controllers” include general-purpose processors and application-specific integrated circuits (ASICs).
The term “about” means to within ±10 percent of the recited value. The terms “roughly” and “significant” refer to within ±25 percent of the recited value, or to within ±25 percent of the maximum value over a recited time interval, respectively.
Introduced above, and described in further detail below, is a self-contained mask system with an automated liquid-droplet dispensing mechanism (ADM) for controlled humidification of inhaled air. The self-contained face mask system (or simply “system”) can include a protective face mask enclosure that is comprised of one or more layers of breathable fabric that are adapted to flexibly conform to the face, when worn by a user to form a primary cavity that is adjacent to the nostrils and mouth of the user of the system. The protective face mask enclosure supports the entire ADM that controllably dispenses droplets of the liquid into the primary cavity for inhalation by the user. Thereby, the face mask system, when light in weight (e.g., less than 100 grams) can be supported entirely by the head and neck of the user while providing for controlled humidification of inhaled air.
The ADM includes several components that are able to work in concert to dispense the droplets of liquid in a controlled fashion. For example, the ADM may include (i) a sensor configured to generate measurements that are representative of a characteristic of air that is exhaled through the nostrils or mouth of the user, (ii) a controller configured to generate a signal in response to determining in real time, based on analysis of the measurements, that an exhalation phase has ended, and (iii) a droplet generator configured to initiate, in response to receiving the signal from the controller, dispensation of liquid from the reservoir into the primary cavity in the form of droplets. Normally, droplet dispensing begins roughly when the inhalation phase commences, so as to humidify air drawn into the nostrils or mouth during the inhalation phase of a breathing cycle (also called a “respiratory cycle”). Moreover, dispensation may end before the inhalation phase concludes, such that the resulting dispense period occurs over only an initial portion of the inhalation phase. Dispensation of droplets only over an initial portion of the inhalation phase helps to ensure that significant numbers of droplets do not remain in the primary cavity following the inhalation phase of a breathing cycle.
At a high level, the sensor is responsible for monitoring a characteristic of air that is exhaled through the nostrils or mouth of the user, either directly or indirectly, so that the controller can monitor the entire breathing cycle. The sensor can take several different forms, however. As an example, the sensor may be an accelerometer that is connected to a flap situated in an exhaust valve in the breathable fabric of the enclosure. In such embodiments, the accelerometer measures motion of the flap, and this motion can be used as an indicator of whether air is being inhaled or exhaled through the nostrils or mouth of the user. As another example, the sensor may be an accelerometer that is mounted to a flexible membrane or substrate embedded into an aperture in the breathable fabric of the mask. In such embodiments, the accelerometer, when attached to the flexible membrane or substrate, can generate measurements that are indicative of motion of the flexible membrane or substrate, and this motion can be used as an indicator of whether air presently is being inhaled or exhaled through the nostrils or mouth of the user. As another example, the sensor may be a temperature sensor that is located along an interior surface of the mask and within the primary cavity. In such embodiments, the temperature sensor can generate measurements that are indicative of the air temperature changes inside the cavity, and these temperatures can be used as an indicator of whether air presently is being inhaled or exhaled through the nostrils or mouth of the user.
The droplet generator also can take several different forms. As an example, the droplet generator may include a vibrating mesh nebulizer (VMN) disc that is operable to induce dispensation of droplets through ultrasonic vibration. Normally, a VMN disc includes (i) a plate with a first side that has one or more ingress holes through which liquid is able to enter the plate and a second side that has one or more egress holes through which the liquid is able to exist the plate and (ii) a vibration element configured to induce movement of the liquid through the plate by ultrasonic vibration. While the ingress hole(s) on the first side of the plate may be fluidly connected to the egress hole(s) on the second side of the plate, these holes do not need to be fluidly connected to one another in a one-to-one relationship. A single ingress hole may be fluidly connected to multiple egress holes (e.g., tens or hundreds) to facilitate dispensation of small droplets. As another example, the droplet generator may include an array of piezoelectric actuators, each of which may have (i) a chamber in which liquid is contained, (ii) a nozzle, and (iii) a piezoelectric element that is configured to displace the liquid in the chamber when a suitable voltage is applied thereto, thereby causing the liquid to be dispensed through the nozzle in the form of a droplet. As another example, the droplet generator may include an array of thermal actuators, each of which may have (i) a chamber in which liquid is contained, (ii) a nozzle, and (iii) a heating element that is configured to heat the liquid to boiling, thereby causing a bubble to form that forces the liquid to be dispensed through the nozzle in the form of a droplet.
As shown in
The respiratory cycle detector 13 can detect and monitor the flow of air inhaled into, or exhaled out of, the respiratory airways of the mask user. For this purpose, the respiratory cycle detector 13 will have at least one sensor 13A that is configured to generate measurements that are representative of a characteristic of air that is exhaled through the nostrils or mouth of the user. The measurements may indicate one or more temporal parameters, including the time (T1) at which the respiratory cycle of the user changes from an exhalation phase to an inhalation phase, the time (T2) during the inhalation phase immediately following T1 at which the rate of change in volumetric flow rate is maximal, and time (T3) during the inhalation phase at which the respiratory cycle of the user changes from the inhalation phase to an exhalation phase.
The timer and controller 15 can be configured to generate a dispense “start” signal at T1, in response to determining, in real time based on analysis of the measurements generated by respiratory cycle detector 13, that an exhalation phase has ended and an inhalation phase has begun. As mentioned above, the ADM 11 also includes a droplet generator 14 that can be configured to dispense droplets of liquid from the reservoir 16 where the individual droplets are exceedingly small so as not to exceed 1 nanoliter in volume. In response to receiving the dispense “start” signal from the timer and controller 15, the droplet generator 14 may initiate droplet dispensation for a period (generally called the dispense period) that coincides with the inhalation phase to humidify air drawn into the nostrils or mouth during the inhalation phase. Moreover, dispensation may end before the inhalation phase concludes, such that dispensation occurs over only an initial portion of the inhalation phase. To do this, a dispense “end” signal can be sent by timer and controller 15 at (T2+y) to droplet generator 14 in response to determining, in real time based on analysis of the measurements generated by respiratory cycle detector 13, that the rate of change in volumetric flow rate, during the inhalation phase of the respiratory cycle, is maximal. Generally, the dispense “end” signal is sent by timer and controller 15 to droplet generator 14 after an adjustable delay time y that allows the user to either increase or decrease the dispense period over which droplets are dispensed during each inhalation phase.
When the face mask system 10 is switched on by the user, for example by pressing a button on, or rotating, the user-interactive on/off switch (that also serves as a timer and controller adjustment device 15A), the default delay time may be zero. The delay time y may be adjusted by the user by interacting with the timer and control adjustment device 15A (also referred to as a “timer and control adjuster”) that is attached to the outer fabric layer 12A of the face mask system 10, as shown in FIGS. 1A, 1B, and 1C. The timer and control adjuster 15A could take on the form of an adjustment knob that can be turned by the user to adjust the duration of the dispense period. The value of the delay time y may be adjustable, for example, between −0.5 and +0.5 seconds. In some embodiments, however, the delay time y is a function of T1 and T2. For example, the delay time may be determined dynamically (i.e., in real time) by timer and controller 15 as follows:
y=x(T2−T1), Eq. 1
where the value of x will generally be between −0.9 and +1.5, though the default value of x may be zero. If the user desires to increase the amount of liquid dispensed, the user can interact with timer and control adjuster 15A in one way (e.g., by turning the adjustment knob clockwise) to either increase x by a predetermined amount (e.g., 0.1) or increase the delay time y by a predetermined amount (e.g., 0.1 seconds). Regardless of the preselected delay parameter settings selected by the user, the timer and controller 15 may send a mandatory dispense “end” signal to droplet dispenser 14 upon receiving information from respiratory cycle detector 13 that time T3 has arrived. In this way, regardless of any preset delay time delays selected by the user, no dispensing may occur during the exhalation phase of a respiratory cycle.
If the user desires to decrease the amount of liquid dispensed, the user can interact with the timer and control adjuster 15A in another way (e.g., by turning the adjustment knob counter-clockwise) to either decrease x by a predetermined amount (e.g., 0.1) or decrease the delay time y by a predetermined amount (e.g., 0.1 seconds). To perform such reductions in dispense time, it may be necessary for timer and controller 15 to send a dispense “end” signal to droplet generator 14 before receiving information from respiratory cycle detector 13, that the time T2 has been achieved. For this purpose, timer and controller 15 may store a running average M of (T2−T1) values. For example, timer and controller 15 may store a collection of data (e.g., 5 or 10) of the most recent (T2−T1) values, or timer and controller 15 may store the (T2−T1) values corresponding to a certain interval of time (e.g., the preceding 5, 10, or 30 minutes). In this way, upon beginning the next inhalation phase, timer and controller 15 can send a dispense “start” signal to droplet generator 14 at T1 (the same as the default condition). Next, however, timer and controller 15 may send a dispense “end” signal to droplet generator 14 at an imputed time T2′ that is calculated from the previous running average M and the new delay setting preselected by the user. For example, if the user selects a 0.4 reduction in x from the default condition (e.g., by turning timer and control adjustment mechanism 15A counter-clockwise four “clicks”) and the running average M of the most recent (T2−T1) values is 0.5 seconds, then the applied change in delay time y=−0.4 (0.5 seconds)=−0.2 seconds. In this case, the timer and controller 15 will send a dispense “end” signal 0.3 seconds after T1, that is, 0.2 seconds less the default value of 0.5 seconds—thereby reducing the dispense period as preselected by the user.
The liquid reservoir 16, as well as the other components of the ADM 11, including timer and controller 15 and power source 17, can be disposed on the outer surface of the outermost layer 12A of mask fabric, the inner surface of the innermost layer 12B of mask fabric, or in interstitial regions between layers 12A and 12B. The respiratory cycle detector 13 and droplet generator 14 of the ADM 11, however, will be located generally on the inner surface of innermost layer 12B of mask fabric and located close to the bottom of the nose (and near the mouth) to allow sensitive detection of the current phase and other parameters of the respiratory cycle (e.g., T1, T2, and T3). Locating respiratory cycle detector 13 and droplet generator 14 near the bottom of the nose also may allow the dispensed droplets to travel unimpeded through cavity 20 to the external openings to the nasal passages (i.e., the nostrils 19) of the user. Alternatively, droplet generator 14 may be placed on an interstitial surface or on the outer surface of the mask fabric provided that a suitable orifice is incorporated into fabric layers 12B and 12A to allow free passage of the droplets from droplet generator 14 through cavity 20 to the nostrils 19 of the user. The respiratory cycle detector 13 may have a similar location provided that a suitable orifice is incorporated into outermost layer 12A and/or innermost layer 12B to allow exhaled air to reach respiratory cycle detector 13 unimpeded.
In some embodiments, the power source 17 for the ADM 11 is a rechargeable battery that is contained within an enclosure 17A (also referred to as a “housing”). A provision for connection to recharging cable 18 advantageously may be provided on the outer surface of the outermost layer 12A of the mask enclosure 12. Alternatively, the power source can be another portable power source, such as a non-rechargeable battery, a bank of capacitors that can be charged by solar cells, etc.
In some embodiments, respiratory cycle detector 13 comprises a primary sensor 13A and a reference sensor 13B. Generally, the primary sensor 13A will be located within the primary cavity 20 of the face mask system 10, close to the respiratory air flow where the primary sensor 13A is able to monitor a physical parameter affected by inspiration and exhalation of respiratory gases of the user. Respiratory cycle detector parameters are further discussed below. The reference sensor 13B will measure substantially the same parameter as the primary sensor 13A, but in contrast, will be located at another location that does not sense the flow of respiratory gases, preferably on the outside surface of the mask. For example, where the measured parameter is temperature, sensors 13A and 13B will be temperature sensors, and the primary sensor 13A will measure temperature of air inside the cavity 20 while the reference sensor 13B will measure temperature of ambient air external to the face mask system 10. Alternatively, where the measured parameter is either pressure or acceleration of a flexible membrane or flap, sensors 13A and 13B can be pressure sensors or accelerometers, respectively.
One goal of the approach to automated liquid dispensing described herein is to minimize the amount of liquid required for adequate humidification of the upper respiratory tract of the user of the face mask system 10, and thereby allow the face mask system 10 to be compact, self-contained, and autonomous from peripheral supporting structures, such as support stands, liquid or vapor feed tubing, motors, compressors, power cords, and the like. Accordingly, the face mask system 10 is made to be practical and convenient to use where the mobility of the user is of paramount importance.
Liquid reagents necessary to fill reservoir 16 of the subject invention may be supplied in kit form together with the self-contained, integrated face mask system 10. The liquid reagents of such a kit can be comprised of sterile or aseptic water. Optionally, the liquid reagents may include substances that provide for, and maintain, the normal composition of the ASLs of the respiratory tract. Such substances without limitation, generally comprise, in their normal physiological cationic forms, sodium (Na+), potassium (K+), calcium (Ca++), magnesium (Mg++), zinc (Zn++), and the like. As counterions, usual substances, in their usual physiological anionic forms, include chloride (Cl−), bicarbonate (HCO3−), phosphate (H2PO4−, HPO4−2, and PO4−3), iodide (I−), tri-iodide (I3−), and the like. Usual uncharged substances, especially those useful to maintain the potential of hydrogen ions (pH) and functionality of the airway surface liquids, include carbonic acid (H2CO3), hypoiodous acid (HOI), hydrochloric acid (HCl), phosphoric acid (H3PO4), ascorbic acid, and the like.
Because a substantial fraction of the dispensed aqueous liquid will evaporate after dispensation but before contact with the airway surface liquid (ASL) of the nasal cavities of a mask user, the concentrations of such substances provided to fill the reservoir 16 generally may be less than the concentrations normally found in the ASL of human nasal cavities. For example, where the mean evaporation of droplet volume is from 90 to 99 percent complete upon reaching the ASL, the concentrations of the substances to be provided in the liquid reagents may be supplied at 10 to 1 percent, respectively, of the concentrations normally found in nasal cavity ASL.
By way of further example, where sodium and chloride generally are present in the ASL at 50 to 150 millimolar (mM), and where the mean evaporation of droplet volume is 90 percent, these substances can be supplied as reagents in the reagent kit between 5 and 15 mM. On the other hand, where hypertonic electrolytes dispensed into the respiratory tract have been found to have beneficial effects, for example in the treatment of cystic fibrosis, then higher concentrations of electrolytes, for example from 50 to 150 mM (or even more), can be provided.
Another important substance in the ASL generally is the iodide anion. Iodide is concentrated from 10- to 50-fold above blood plasma levels by a sodium/iodide transporter protein bound to the cell membrane on the side of the airway epithelial cells facing the blood stream. The epithelial cells then release the concentrated iodide to the ASL via a nonspecific anion channel bound to the cell membrane on the opposite side of the cells (i.e., the side adjacent the ASL). Blood plasma iodide levels generally range from 0.5 to 2 micromolar (μM), and normal levels in the ASL generally range from 5 to 100 μM. Accounting for the 90 percent evaporation upon droplet dispensing, iodide therefore may be supplied in the reagent kit at between 0.05 and 10 μM. Normally, iodide in such reagent kits is supplied at between 0.5 and 1.0 μM, though iodide could be supplied in such reagent kits at higher or lower levels.
When respiratory epithelial cells are attacked by viruses or microbial organisms, these cells respond defensively by oxidizing the previously concentrated iodide in the ASL to hypoiodous acid (HOI) and elemental iodine (I2). These oxidized iodine species appear not to attack the invading organisms directly, but instead appear to react biosynthetically to form specific iodinated compounds that interfere with the replication of viruses and bacteria. Therefore, under circumstances where there is a heightened concern, or increased risk of infection by a pathogen due to an ongoing epidemic, pandemic, crowded environmental conditions, or the like, users of the mask system 10 may want to utilize a reagent composition that provides for and maintains the ASL with a composition that is optimal for defense against such pathogens. In such cases, various oxidized iodine species may be provided in the reagent kit. The oxidized iodine species may be selected from several different forms, including hypoiodous acid (HOI), elemental iodine (I2), or the tri-iodide anion (I3−) that comprises one molecule of elemental iodine and one molecule of iodide anion, or the like. All three of these oxidized iodine species are in chemical equilibrium, so it is relatively inconsequential which form is dispensed. It is important, however, that the oxidized species be stored in a stable form prior to dispensation by the droplet generator 14. The tri-iodide anion species may be the preferred species of oxidized iodine in some embodiments because it is highly stable and unreactive in storage, but upon dilution it dissociates into the more reactive elemental iodine (I2) species, which in turn is in equilibrium with the even more reactive hypoiodous acid (HOI) species which appears to be the most effective at undergoing biosynthetic reactions that form substances that inhibit viral and bacterial replication. Customarily the tri-iodide anion will be supplied, for dispensing from a liquid reservoir 16, as the sodium or potassium salt at a final diluted concentration between 0.05 and 2.5 μM. More typically, the tri-iodide anion will be supplied at between 0.25 and 1.0 μM.
To store liquid reagents that are more stable in their concentrated form (using the tri-iodide anion as an example), the following approach may be used. The tri-iodide anion species can be supplied in a stable concentrated form, for example, as the well-known tincture of iodine that is an equimolar mixture of elemental iodine and the iodide anion. Generally, the composition of the tincture is about 2 percent iodine by weight and about 2.4 percent sodium iodide by weight dissolved in about 50 percent water and 50 percent ethanol. Alternatively, an equimolar ratio of iodine and iodide can be achieved by using about 2 percent iodine and about 2.6 percent potassium iodide (and similarly for other soluble iodide salts). As shown in
The volume of individual dispensed droplets customarily will be in the range of 1 attoliter (10−18 liter) to 1 nanoliter (10−9 liter). When spherical, the droplets generally will be from 0.1 to 100 micrometers (μm) in diameter. More typically, the droplets will be between 0.5 and 50 μm in diameter. Droplets dispensed by the droplet generator 14 of the face mask system 10 that are larger than 50 μm in diameter have a high probability of being deposited on the first surface that is encountered, such as on the surfaces of the nasal passages of the face mask user. Smaller droplets, in contrast, have an increased probability of reaching the lower respiratory tract of the face mask user, including the terminal alveoli of the lungs. It is generally accepted that droplets between 1 and 5 μm in diameter are most useful for delivery of dissolved substances to the alveolar tissues. Droplets even smaller will have the high probability of disappearing completely into the vapor phase (i.e., evaporating), and thus will be useful for the purposes of providing humidity but not for transporting dissolved solutes deep into the respiratory tract.
For purposes of delivering only water vapor (humidity) to the respiratory tract, the broadest range of droplet sizes from droplets that are about 0.1 μm in diameter (about 0.5 attoliter in volume) to about 100 μm in diameter (about 0.5 nanoliter in volume) may be used. Several types of droplet generators can dispense droplets in this size range, including vibrating mesh nebulizer (VMN) dispensers, piezoelectric inkjet (PIJ) dispensers, and thermal inkjet (TIJ) dispensers. Inkjet dispensers generally are used to dispense droplets from nozzles for printing applications, usually in the 1-100 picoliter range, and generally are driven at frequencies of 1-50 kilohertz (kHz) for repeated dispensation from each nozzle. In contrast, VMN dispensers can operate at higher frequencies (e.g., 100 kHz or more), thereby providing for the desired liquid dispensing rates (as measured in liquid volume dispensed per unit time) while still making it possible to deliver much smaller droplets. Droplets as small as 0.1 μm in diameter (0.5 attoliter in volume) may be formed and dispensed by a VMN dispenser by making correspondingly small holes in the plate (also referred to as the “disc”) through which liquid is directed. Larger holes in the plate will allow for the formation of larger droplets that can then be dispensed. The VMN dispensers are highly versatile and provide for dispensing a wide range of droplet sizes over a wide range of liquid volumetric dispense rates. The VMN dispensers also operate with relatively low power and are light in weight and therefore are generally preferred as the droplet generator 14.
In
The kinetic energy of the dispensed droplets 32, as well as the force of gravity, will affect the path of the dispensed droplets 32. In embodiments where PIJ dispensers or TIJ dispensers are used to dispense the droplets, the initial velocity v of the dispensed droplets generally will be between 5 and 20 meters per second (m/sec). Droplets with mass m and mean velocity v will have kinetic energy of ½ mv2 and will be able to travel upward against the acceleration of gravity g tor a maximum distance of h, where ½ mv2=mgh. Solving for the maximum distance h shows that the droplets may be able to travel upwards as high as 5 meters or more. Air resistance, however, creates drag that generally limits the distance of upward travel to less than 5 meters. The effect of drag from air resistance is insignificant compared to the kinetic energy of dispensed droplets having volumes at least in the picoliter range, especially for short (e.g., 0.5-3.0 cm) distances from the droplet generator 14 to the nostrils 19 of the nose of the user. Therefore, the kinetic energy of larger dispensed droplets (e.g., those exceeding one picoliter in volume) will be important to their direction of travel. Consequently, PIJ and TIJ dispensers must be carefully positioned and aimed. Conversely, for smaller droplets in the femtoliter and sub-femtoliter ranges that are dispensed by VMN dispensers, the effect of air resistance (drag) is much greater. With these smaller dispensed droplets, the effects of the airflow stream 18, during inhalation, as shown in
In another embodiment, sensor 13A is paired with a reference sensor 13B. For example, if sensor 13A is a temperature sensor as discussed above, then sensor 13B may be a reference temperature sensor that is situated outside of the mask and positioned to monitor the environmental temperature (also referred to as the “ambient temperature”). Reference sensor 13B can send a reference signal to the timer and controller 15 that can be compared to the signal produced by temperature sensor 13A that is disposed within the primary cavity 20 within the mask. The reference signal may be representative of a stream of sequential temperature measurements generated by reference sensor 13B, and advantageously averaged over several seconds or minutes (e.g., to minimize noise). The signal generated by sensor 13A situated within primary cavity 20 of the face mask enclosure 12 may also be representative of a stream of sequential temperature measurements in order to minimize noise, but in contrast, must be averaged over a much shorter time period (e.g., from 1 to 200 milliseconds for respiratory cycles of usual periods from roughly 0.5 to 3 seconds in duration). Advantageously, the reference sensor 13B may be used to reduce environmental variations to further improve the accuracy of the determination made by the timer and controller 15 that triggers the beginning and end of droplet dispensing by droplet generator 14. In embodiments where the respiratory cycle detector 13 relies on analysis of temperature measurements (e.g., temperature measurements generated by sensor 13A and reference sensor 13B) to determine when dispensation should be triggered by the timer and controller, the triggering can be predetermined to occur by a ratio of the signals sent by sensor 13A and 13B to the timer and controller. For example, triggering can be predetermined to occur upon a fractional approach (e.g. a ratio in the range of 2 to 10 percent) from the highest exhalation temperature measured by sensor 13A to the environmental temperature measured by reference sensor 13B. For example, if (i) sensor 13B measures the environmental temperature to be 23° C., (ii) the maximum exhalation temperature measured by sensor 13A within the primary cavity 20 of the mask is 37° C. (i.e., producing a difference of 14° C.), and (iii) the predetermined fractional approach is set to be 7.14 percent, then droplet dispensing would be triggered by the timer and controller when the temperature measured by sensor 13A changes from 37° C. to 36° C. (i.e., 1/14th or 7.14% of the temperature difference). For usual respiratory cycles of humans (e.g., occurring at about 0.5 Hz), the greatest signal-to-noise ratio will be achieved when sensor 13A has a response time faster than 0.2 seconds (e.g., between 50 and 200 milliseconds). When this is the case, the fractional change needed for triggering of droplet dispensing by the timer and controller may be at the higher end of the range (e.g., near 10 percent). Alternatively, when the response time of sensor 13A is relatively slow (e.g., greater than 1 second), then the fractional change needed for triggering of droplet dispensing may be at the lower end of the range (e.g., near 2 percent). Hence, a faster time response of sensor 13B can improve the signal-to-noise ratio, as received by the timer and controller 15, which results in improved precision, with less hysteresis (i.e., less response delay), for triggering of dispensing by droplet generator 14. Electronic noise reduction techniques may be applied by timer and controller (as discussed above) to further increase the signal-to-noise ratio. For example, the incoming signals from the respiratory cycle detector can be averaged over 1 to 100 milliseconds, thereby reducing noise in the data. As another example, a Savitzky-Golay filter may be applied to the incoming signals over 1 to 100 millisecond intervals. The duration of the droplet dispensing sequence triggered by the timer and controller (i.e., the dispense period) usually will be for a duration between 0.05 and 0.8 seconds (and more typically between 0.1 and 0.5 seconds). To allow for longer or shorter dispense periods, the timer and control adjuster 15A may be attached to an exterior surface of the outermost layer 12A of the mask enclosure (as shown in
Several alternative means are available for detecting the inhalation and exhalation phases of the respiratory cycle. For example, sensor 13A could be a differential pressure sensor that compares the pressure within the primary cavity 20 inside of the mask enclosure to the pressure outside of the mask enclosure (thereby performing the functions of both sensors 13A and 13B). For such differential pressure comparisons, a similar algorithm to that described above for temperature changes by sensors 13A and 13B could be used by the timer and controller 15 to trigger the beginning of a sequence of droplet dispensing by droplet generator 14. Other alternative sensors whose outputs could be used to determine the instant phase of the respiratory cycle of the user of the mask system include nasal capnometers, nasal pressure transducers, accelerometers including abdominal accelerometers, transpulmonary electrical impedance monitors, peritracheal microphones, sensors for photoplethysmography, and the like.
Power consumption by sensors such as accelerometers and temperature sensors (e.g., thermocouples or thermistors) can be very low. Low consumption of power allows power source 17, as shown in
In some respiratory cycle detector embodiments, an accelerometer 103 can be attached to a movable flap (120A and 120B) instead of to the flexible membrane 104 that is shown in
The electrical signal can be processed to “pre-arm” the timing and controller 15. Following the pre-arming, the timer and controller can send a signal to the droplet dispenser to begin droplet dispensing upon return of the movable flap to its normally closed position 120A, whereupon the light beam 116 again is blocked from reaching photodetector 118 and the electrical signal from the photodetector 118 that is sent to the timer and controller 15 is terminated. Termination of the electrical signal sent to the timer and controller, following the pre-arming event, may then prompt the timer and controller 15 to trigger the droplet dispenser to dispense a sequence of droplets for the dispense period, the length of which may be for either a predetermined period or a period determined by a computed algorithm (as discussed previously).
To further improve the signal-to-noise ratio of the photo-interrupter mechanism, the light source 114 can be modulated at a predetermined frequency (e.g., 10 kHz). The light source 114 may be, for example, a light-emitting diode (LED) or another illuminant. In this case, the photodetector 118 may have an electronic bandpass filter that provides an output signal that is substantially proportional to the modulated light only (and independent of continuous light that creates a direct current or light that is modulated at other frequencies). Exhaled air that passes through the exhaust valve 112 and actuates the movable flap optionally may be filtered by a porous fabric filter material 119. Additionally or alternatively, the exhaled air may be directed downward into the clothing of the user by a material 119 that facilitates the removal of respiratory droplets from the exhaled air prior to being expelled into the ambient environment.
The timer and controller 15, as shown in
In some embodiments, the timer and controller 15 comprises a solid-state microprocessor that includes memory to enable storage of firmware- or software-implemented instructions. The microprocessor may be able to emulate the functions of comparators, transistors, monoflops, and flipflops. Microprocessors can further process the input signal from the respiratory cycle detector 13 to reduce noise. Because predetermined parameters can be stored in the memory of a such a microprocessor and changed when desired, such a microprocessor can facilitate changing operational parameters, from time to time, to improve operation of the droplet generator 14 within the mask system 10.
A microprocessor also may be able to facilitate the operation of certain types of alternative droplet generators, including TIJ or PIJ dispensers. A combination of a clock, a counter, and a demultiplexer can be used to send pulses in sequence to the driver of a TIJ dispenser or a PIJ dispenser. The counter may be responsible for counting clock cycles and then storing information on how many clock cycles have passed. This information then can be used by the microprocessor to send the “start” and “end” signals, as determined by the timer and controller, to a demultiplexer that, based on information in the “start” signal, addresses a selected output (e.g., to begin the dispense period at a selected nozzle of a TIJ or PIJ dispenser). Other aspects for controlling and driving TIJ and PIJ dispensers, as adapted for use in the instant face mask technology, are described below.
As discussed above, the droplet generator 14 may be responsible for commencing and then concluding dispensation of liquid droplets from a reservoir 16 based on signals received from the timer and controller 15. Generally, dispensation begins when the inhalation phase commences, so as to humidity air that is drawn into the nostrils or mouth of the user during the inhalation phase. However, dispensation may end before the inhalation phase concludes, such that dispensation occurs over only an initial portion of the inhalation phase. Such an approach can help to ensure that a cavity defined by the innermost layer 12B of the face mask fabric and the face of a mask user does not become “over-humidified,” which could result in liquid water saturating the breathable fabric layers 12A and 12B of the face mask system 10, rendering it inoperable.
The droplet generator 14 can take several different forms depending on the goals and constraints of the face mask system 10. These different forms are further discussed below. Regardless of its form, the droplet generator 14 generally is configured to direct a sequence of droplets 32 towards the nostril openings 19 of the nasal passages 33 of the mask user. Liquid can be dispensed through holes in a plate by applying pressure by vibration, for example, by a VMN dispenser. Alternatively, liquid can be dispensed through nozzles by inducing a volume change, for example, by a PIJ dispenser or a state change (e.g., from liquid to gas), for example, by a TIJ dispenser.
As an example, in embodiments where small droplets (e.g., not exceeding one nanoliter in volume) are desired, the droplet generator 14 may comprise a VMN dispenser 40 that includes a plate 43, as shown in
As shown in
The diameter of the generated droplets is approximately the same as the diameter of the holes on the liquid-dispensing side 42 of the plate 43. Suitably small, tapered holes, with their smallest diameter between 0.5 to 2 μm, can be employed to predetermine the size of the droplets. Vibration of the plate 43 can be initiated by a vibration element, such as a ring-shaped piezoelectric transducer 48 that is located around the perimeter of the plate 43 as shown in
In a preferred embodiment, the VMN dispenser comprises a plate 43 that is 16 mm in diameter with an annular or ring-shaped piezoelectric crystal 48 located along its perimeter that is roughly 4 mm wide. The piezoelectric crystal 48 can be electrically driven by the oscillator as discussed above. A precision timing circuit, such as a NE555 timing device manufactured by Texas Instruments, together with a tuning resistor circuit, can be used to tune the oscillator to the desired resonant frequency. The NE555 timing device may also have associated trigger circuitry that can be used for synchronizing the output of the VMN dispenser to the respiratory cycle of the user. A conventional power converter, such as the MC34063a DC-to-DC power converter manufactured by Texas Instruments, may be suitable for boosting the lower voltage signal (e.g., at 16 volts) to the higher voltage signal (e.g., at 50 volts) needed to drive the piezoelectric crystal. The plate 43 may consume 1-1.5 watts (W) of power when it is generating aqueous liquid droplets at a rate of approximately 22 mg/sec. Therefore, to dispense a full reservoir of 36 grams of aqueous liquid, the energy required is about (1-1.5 W)·36 g/(22 mg/sec)=1.6-2.5 kJ.
A power source 17 that is able to provide at least 1-1.5 W of power can be designed and/or selected for the face mask system 10. Options include rechargeable lithium-ion (Li-ion) batteries and lithium-polymer (Li-polymer) batteries with an output voltage between 3.0 and 3.7 V. At this voltage, the required 1.6-2.5 kJ of energy can be supplied by 127-190 milli-ampere hour (mAh) of current capacity. Li-polymer batteries that meet the power and energy requirement include the DTP502535 battery manufactured by DataPower Technology that has an energy capacity of 400 mAh and a peak discharge current of 400 milliampere (mA) (1.36 W). Similarly, the LIPO552530 battery manufactured by PK Cell has an energy capacity of 350 mAh and a peak discharge current of 350 mA (1.3 W).
The droplet generator 14 preferably dispenses about 5 milligram (mg), with an adjustable range from 1 to 20 mg, of liquid water droplets during each respiratory cycle of a user of the face mask system. Therefore, with a dispense rate of 22 mg/sec, the VMN dispenser will require a droplet-dispensing sequence, or dispense period, that is about 0.23 seconds in duration. If an individual user desires a lessor, or a greater, quantity of dispensed liquid droplets during each respiratory cycle, the timer and controller adjustment mechanism 15A will decrease, or increase, the dispense period of the liquid droplet dispensing sequence during each respiratory cycle. The maximum duration of the dispense period during a particular respiratory cycle will be approximately the total length of the inhalation portion of that respiratory cycle, roughly 1 second.
In addition to the placement of one or more control mechanisms (e.g., timer and controller adjuster 15A) on an outermost layer 12B of the face mask system, the user may be able to control the rate of droplet dispensing remotely and wirelessly, for example, through a computer program (e.g., a mobile application) executing on a computing device (e.g., a mobile “smart” phone). Operation times, dispense power, and dispense sequence durations may be remotely selected through the computer program. Remote control communication between the face mask system 10 and the computing device may be performed through standard wireless communication protocols, such as Bluetooth, ZigBee, WiFi, and the like provided that the appropriate receivers are incorporated into the face mask system 10. A Near Field Communication (NFC) protocol could be used provided that the computing device is moved to within a few centimeters of an NFC receiver appropriately placed within the face mask system 10 (e.g., on the outer surface 12A of the face mask enclosure near the timer and controller 15).
As mentioned above, embodiments of the face mask system 10 could include PIJ dispensers or TIJ dispensers instead of VMN dispensers in some instances. At a high level, PIJ dispensers force liquid droplets from a nozzle by reducing the volume of an adjacent chamber through the application of an electric field to a piezoelectric material. TIJ dispensers, meanwhile, force liquid droplets from a nozzle by heating liquid in an adjacent chamber to boiling, so that a gas bubble is formed that forces a liquid droplet from the nozzle. PIJ and TIJ dispensers are commonly fabricated by photolithographic techniques that are used to pattern and etch physical structures, such as microchannels and microchambers, into silicon.
Advantageously, the energy required to eject a droplet from a PIJ dispenser generally is much smaller than the energy needed to eject a droplet from a comparable TIJ dispenser because the PIJ dispenser does not heat the liquid contained therein. The energy required for dispensing by a PIJ dispenser is largely attributable to the increased kinetic energy of an ejected droplet 69. For aqueous droplets with a volume of about 10 picoliters, that are ejected at a velocity of about 10 m/sec, the kinetic energy is approximately 1 nano-joule. This is roughly 10 times less energy than is required to dispense the same volume of water by a VMN dispenser and roughly 1,000 times less energy than is required to dispense the same volume of water by a TIJ dispenser. Further information regarding PIJ dispensers can be found in U.S. Pat. No. 5,946,012, titled “Reliable High Performance Drop Generator for an Inkjet Printhead,” which is incorporated by reference herein in its entirety.
A PIJ dispenser, similar to those manufactured by Dimatix Print Systems for inkjet printing applications, may be suitable for use in embodiments of the face mask system described herein. Generally, PIJ dispensers are configured to eject a droplet of liquid when a voltage in the range of 15 to 50 V is applied to its piezoelectric element. The instantaneous power needed to dispense a 10-picoliter droplet is normally about 1 mW. Available nozzle sizes for PIJ dispensers generally provide for dispensing droplets that range in volume from 1 to 10 picoliters. The dispense speed can be as high as 80 kHz, which reduces the number of nozzles that would be needed in a given face mask system. Simply put, when droplets of liquid can be emitted at high frequencies (e.g., with a PIJ dispenser), a high number of nozzles (e.g., hundreds or thousands) may not be necessary. In contrast, TIJ dispensers generally operate at lower frequencies (e.g., roughly 20 kHZ or less), and therefore more TIJ nozzles will be needed to eject the same number of droplets during an inhalation phase of a respiratory cycle.
The TIJ dispenser, however, may be suitable as droplet dispensers 14 in some embodiments of the face mask system 10. Further information regarding TIJ dispensers can be found in U.S. Pat. No. 4,296,421, titled “Ink Jet Recording Device Using Thermal Propulsion and Mechanical Pressure Changes,” and U.S. Pat. No. 4,490,728, titled “Thermal Ink Jet Printer,” which are incorporated by reference herein in their entirety. TIJ dispensers are similar to PIJ dispensers but consume considerably more energy as mentioned above. Generally, however, TIJ dispensers are less expensive to manufacture, so TIJ dispensers may be useful in embodiments where cost is relevant.
A TIJ dispenser like those manufactured by Hewlett Packard for inkjet printing applications may be suitable for use in embodiments of the face mask system described herein. As an example, the TIJ dispenser may be similar to the HP45 cartridge that has 300 nozzles with 52 electrical pads, as well as heating resistor values of 40 ohms. Switching transistors can be integrated onto a silicon substrate (also referred to as the “chip”), together with the filling and dispensing channels and heating resistors, so that each resistor is addressable from at least one of the 52 electrical pads. The TIJ dispenser may be able to dispense droplets at frequencies between 1 and 20 kHz. Implementing TIJ dispensers within a face mask system requires special attention to the power and energy that must be supplied by power source 17. Normally, dispensing requires a nominal 12 volt pulse that draws 300 mA of current for 2 microseconds. Therefore, the instantaneous power required is about 3.6 W (300 mA×12 volts), and the energy required for dispensing each 30 picoliter droplet is about 7.2 microjoules (3.6 W×2 microseconds). The total amount of energy needed to dispense the entire aqueous liquid volume from a 36 ml reservoir is about 8.6 kilojoules (7.2 microjoules/30 picoliters×36 ml). A 3-volt CR2 Li-ion rechargeable battery (3 W, 8.6 kJ) that weighs between 10 and 11 grams may be selected as the power source 17 in embodiments where the face mask system includes a TIJ dispenser. The CR2 Li-ion battery may support operation of one nozzle of a TIJ dispenser at a time. Interleaving the operation of several (e.g., between 10 and 50) nozzles, one at a time, can provide for roughly 500,000 30-picoliter droplets to be dispensed over the course of a second.
The three sets of horizontal lines in
The foregoing description of various embodiments of the technology has been provided for the purposes of illustration and description. It is not intended to be exhaustive or to limit the claimed subject matter to the precise forms disclosed.
Many modifications and variations will be apparent to those skilled in the relevant art. Embodiments were chosen and described in order to best describe the principles of the technology and its practical applications, thereby enabling others skilled in the relevant art to understand the claimed subject matter, the various embodiments, and the various modifications that are suited to the particular uses contemplated.
This application is a continuation of U.S. application Ser. No. 17/496,663, filed Oct. 7, 2021, which is incorporated by reference hereto in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| Parent | 17496663 | Oct 2021 | US |
| Child | 17813450 | US |
