Patent Application
20170065208
The present invention relates generally to monitoring devices used to measure pulmonary functions, and more particularly to spirometry testing and testing for nitric oxide, as well as other markers, associated with monitoring respiratory medical conditions.
Respiratory diseases are some of the most common disorders in the world. Such respiratory diseases included conditions such as COPD, asthma, cystic fibrosis and pulmonary fibrosis. Chronic obstructive pulmonary disease (COPD), for example, affects millions of people and is responsible for extensive morbidity and mortality in the United States. COPD is a term used to describe chronic lung diseases characterized by progressive development of airflow limitation that is usually not fully reversible with medication. The common symptoms of COPD include breathlessness, wheezing and a chronic cough.
Asthma is another example of a chronic lung disease with symptoms similar to COPD, such as breathlessness and wheezing, but etiologically distinct from COPD. Asthma is a prevalent health care problem; it affects millions in the United States and around the world. About 40% of patients with asthma can be classified as having moderate to severe asthma and would benefit from more frequent monitoring of their airway inflammation. Although COPD and asthma require different treatments, test results for COPD and asthma often overlap.
Asthma in particular is characterized by an inflammatory reaction in hyper-reactive airways that restrict airflow into the lungs. In recent years, measurement of exhaled nitric oxide (eNO) has been shown to be a non-invasive and complementary tool to other pulmonary function tests in assessing airway inflammation, specifically in subjects with asthma. Accordingly, the presence of eNO has become a well-known, globally accepted biomarker for airway inflammation.
Nitric oxide is produced endogenously in cells by NO synthase and secreted by eosinophils in the distal alveoli. Its production is increased in response to inflammatory cytokines (which is associated with asthmatic episodes), and exhaled NO is thought to be an indirect measurement of airway eosinophilic inflammation. Thus, nitric oxide exhaled from the lower airways (e.g. non-nasal airways) can be correlated with the degree of airway inflammation. Patients with asthma have high levels of NO in their exhaled breath. Nitric oxide levels increase prior to the presence of clinical symptoms and its levels decline in response to appropriate therapy as airway inflammation subsides. These two characteristics make this an ideal biomarker for managing asthma status. For this reason, in 2011, the American Thoracic Society (ATS) issued new guidelines recommending the measurement of exhaled nitric oxide for the diagnosis and management of asthma. A diagnosis of asthma can be made when the level of nitric oxide in exhaled breath exceeds 50 ppb. High eNO levels are also associated with other inflammatory respiratory conditions.
In diagnosing respiratory diseases, a series of tests are routinely conducted. A common pulmonary function test (PFT) is spirometry, which measures obstruction of an individual's airway. A decreased maximum/forced lung exhalation rate often suggests airway obstruction. Results from the spirometry test can be used to estimate lung function and aid in assessing respiratory diseases and conditions. In the spirometry test, the patient expels air forcefully into a device to measure the amount (volume) of air or the air speed (flow) exhaled in one complete breath. The commonly used techniques to measure eNO require a subject to exhale into a device containing an NO sensor (online) or into a reservoir that can be analyzed later (offline). Since the concentration of eNO is inversely related to flow rate where lower exhalation rates allow more time for eNO to enter from the airway, the eNO test requires a user to exhale at a steady flow rate, normally at 50 ml/sec. As describe above, the level of eNO, measured in parts per billion (ppb), is significantly higher among asthmatic patients compared to healthy individuals.
Although the spirometry test is a common method of measuring airflow obstruction and can facilitate the monitoring of pulmonary disorders, the overlapping results in some conditions of COPD and asthma limit the use of the spirometry test alone for differentiating COPD from asthma. Additional investigations employing eNO tests, CT scans or pulse oximetry are also commonly employed to aid in assessing pulmonary diseases and conditions.
There are a number of challenges in current pulmonary function testing. Pulmonary function tests employ devices that are typically large and require the patient to be present in the physician's office or in the hospital for the tests. Moreover, the tests require separate devices, since in assessing respiratory disorders and conditions, separate measurement protocols are required for spirometry and for eNO testing. Typically, NO is measured in a clinical setting at a hospital or a physician's office for diagnostic purposes. The devices are expensive to purchase and maintain. Patients who have the most to gain from regular NO monitoring do not have regular access to accurate NO measuring equipment without frequent visits to their doctors. Thus, for at least the millions of people with moderate to severe asthma, there is a need for a cost-effective device that allows weekly or daily NO monitoring at home
Another challenge in current standard pulmonary function testing is the accuracy and efficiency of the testing. An effective eNO test would be complimentary to the standard tests, but there is a dearth of inexpensive sensors capable of detecting the minute amounts of NO (typically measured in parts per billion) present in exhaled air. Moreover, NO sensors need to provide an accurate NO measurement in the presence of other possibly interfering gas components, including water and carbon dioxide (CO2). A further challenge for NO measurement is the difficulty in distinguishing between nitric oxide (NO) and nitrogen dioxide (NO2) in a patient's breath. That is, the gas introduced from the patient's breath typically has concentrations of NO, NO2, carbon monoxide (CO), and oxygen (O2). Traditional sensors are often unselective or incapable of distinguishing between the two main NOx components of interest, NO and NO2, resulting in erroneous readings.
Thus, it would be desirable and advantageous to provide an accurate, efficient and portable respiratory monitor capable of conducting multiple pulmonary function tests, as well as other associated measurements, in a single device. In some applications, it would also be desirable and advantageous to provide a compact monitor with low power consumption. It would also be desirable and advantageous to provide such a device that further allows for the remote monitoring of testing data, thereby avoiding the necessity for patients to make trips to doctor offices and hospitals. Additionally, it would be desirable and advantageous to provide such a respiratory monitor that allows for correlation of respiratory data to other relevant environmental data that can be presented in an efficient and easily understandable format.
The present invention relates to respiratory monitors that incorporate nitric oxide detectors wherein exhaled breath from a user enters the detection device via a sample inlet that leads to a flow pathway within the detection device. In the flow pathway, one or more humidity equilibrators equilibrate the humidity of the breath sample in the flow pathway to the humidity of the ambient air to produce a humidity equilibrated breath sample. A catalytic filter in the flow pathway then receives the humidity equilibrated sample and generates a known equilibrium mixture of NO and NO2 from NOx. A NOx sensor positioned in the flow pathway then measures the NOx concentration in the sample. A controller thereafter calculates the total NO in the sample based on the measured NOx concentration and the known equilibrium.
In another aspect of the invention, one or more respiratory functions can be measured in a single device. The monitoring device comprises a housing that contains an inlet section positioned in the housing and configured to receive a gaseous sample, e.g., air expelled from a subject's lungs. A measuring section is located adjacent to the inlet section, along with a flow detection component positioned within the inlet section and configured to measure the flow rate of a gaseous sample entering the inlet section. An adjustable airflow restriction component is positioned upstream of the flow detection component. An adjustable partition can also be positioned downstream of the flow detection component for further directing and restricting air flow in the device. At least one gas detection sensor is positioned in the measuring section and configured to measure the presence of a predetermined gas contained in a gaseous sample received in the inlet section.
In another aspect of the invention, the gas detection sensor includes at least one electrochemical nitric oxide (NO) sensor configured to detect exhaled NO at aperture-directed flow rates.
The device can further include an optical sensor configured to perform blood flow measurements, and also include an accelerometer configured to perform respiratory measurements.
The device can also include at least one oxygen (O2) sensor configured to detect O2 levels in exhaled breath.
If desired, the device can further include an electronic controller integrated with the device and electronically coupled with the sensors. The controller can be configured to enter user information, execute programs, receive signals from the sensors and transmit data to a selected network or other remote locations.
In another aspect of the invention, a mouthpiece for users of monitoring devices permits fresh air to be inhaled through the mouthpiece via a dedicated pathway, and exhaled through the mouthpiece and into the monitoring device via a separate dedicated pathway. One or more filtering agents, filters or filtering media can be incorporated into one or both of the pathways to permit the screening of certain gaseous components, for example, NOx.
In another aspect of the invention, spirometry and nitric oxide measurements can be correlated with selected environmental factors and presented in an easily understandable format. The devices described herein can be adapted to communicate measurements by wired or wireless technology and maintain data in the cloud for remote monitoring, access, and predictive analytics.
In some embodiments, the invention provides a gas sensor comprising a reactor portion, a sensor portion, one or more connecting flow channels between the reactor and sensor portions, and separate heating elements attached to each of the reactor and sensors. In other embodiments, the invention provides a gas sensor comprising a reactor portion, a sensor portion, one or more connecting flow channels between the reactor and sensor portions, and a heating element with heat separation or conduction media disposed between the reactor and sensor.
The reactor and sensor assembly of the present invention may include a plurality of chambers. For example, a first chamber may comprises a catalytic filter adapted to catalyze the formation of an equilibrium mixture of NO and NO2 from NOx in an incoming gas stream. A second chamber located downstream from the first chamber comprises a sensor element adapted to contact the equilibrium mixture of NO and NO2. The sensor element comprises a sensing potentiometric electrode and a reference potentiometric electrode. A gas conduit connects the first and second chambers. A heating element is disposed between the catalytic filter and sensor element. The heating element comprises a single heat source and is adapted to distribute heat to the first and second chambers. The catalytic filter and sensor element are each maintained at different temperatures using the heating element. In some embodiments, the first gas chamber is disposed below the second gas chamber, and the gas conduit comprises external tubing connecting the first and second gas chambers. In other embodiments, the assembly includes a ceramic package and pins extending from a lower portion of the ceramic package. The ceramic package forms at least a portion of a housing around the first and second chambers, and the pins are adapted to electronically connect the sensor element to a printed circuit board.
In yet other embodiments, reactor and sensor assembly of the present invention provides a plurality of zones through which breath gas may flow. In some embodiments, the assembly comprises a base platform; a plurality of interlocking support structures disposed on the base platform to define a serpentine gas flow path. The support structures comprise a first surface; a second surface disposed below the first surface; and a third surface disposed below the second surface. The assembly further includes a catalytic filter disposed on an upper side of the third surface, the catalytic filter adapted to catalyze the formation of an equilibrium mixture of NO and NO2 from an incoming gas stream; and a sensor element disposed on an underside of the third surface, the sensor element adapted to contact the equilibrium mixture of NO and NO2. The sensor element comprises a sensing potentiometric electrode and a reference potentiometric electrode. The assembly also includes a heating element disposed between the catalytic filter and sensor element. The heating element comprises a single heat source adapted to distribute heat to the catalytic filter and sensor element. The catalytic filter and sensor element are each maintained at different temperatures using the heating element.
In other embodiments, the present invention provides an apparatus for determining total NOx, including NO and NO2 concentrations from a gas stream that comprises a housing; a substrate disposed within the housing; a catalytic filter disposed on the substrate; a sensor element disposed on the substrate downstream from the catalyst filter; and a heating element disposed within the substrate below the catalytic filter and sensor element. The catalytic filter is adapted to catalyze the formation of an equilibrium mixture of NO and NO2 from an incoming gas stream. The sensor element is adapted to contact the equilibrium mixture of NO and NO2 and comprises a sensing potentiometric electrode and a reference potentiometric electrode. The heating element comprises a single heat source and is adapted to distribute heat to the catalyst filter and sensor element. Advantageously, the catalytic filter and sensor elements are each maintained at different temperatures using the heating element.
The present invention further provides for an apparatus for determining total NOx concentration, including NO and NO2 concentrations from a gas stream comprising a housing; a gas inlet positioned in the housing; and a measuring section. The gas inlet section comprises a flow detection component; an adjustable flow-restriction component positioned downstream of the flow detection component; and an adjustable partition positioned downstream of the flow detection component. The measuring section includes one or more of the reactor and sensor assemblies described below, located adjacent to the inlet section and in fluid communication with the inlet.
Embodiments, which use the principles of the present invention, are illustrated with reference to the accompanying drawings.
As used herein, the terms “comprises,” “comprising,” “includes,” “including,” “has,” “having,” or any other variation thereof, are intended to cover a non-exclusive inclusion. For example, processes, methods, articles, or apparatuses that comprise a list of elements are not necessarily limited to only those elements but may include other elements not expressly listed or inherent to such processes, methods, articles, or apparatuses. Further, unless expressly stated to the contrary, “or” refers to an inclusive “or” but not to an exclusive “or.” For example, a condition A or B is satisfied by any one of the following: A is true (or present) and B is false (or not present), A is false (or not present) and B is true (or present), and both A and B are true (or present).
Also, use of “a” or “an” are employed to describe the elements and components of the invention. This is done merely for convenience and to give a general sense of the invention. This description includes one or at least one and the singular also includes the plural unless it is obvious that it is meant otherwise.
Unless otherwise defined, technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Although methods that are similar or equivalent to those described herein can be used in the practice or testing of the present invention, suitable methods and materials are described herein. All publications, patent applications, patents, and other references mentioned herein are incorporated by reference in their entirety. In case of conflict, the present specification, including definitions, will control. In addition, materials, methods, and examples are illustrative only and not intended to be limiting.
In the following description, numerous specific details, such as the identification of various system components, are provided to understand the embodiments of the invention. One skilled in the art will recognize, however, that embodiments of the invention can be practiced without one or more of the specific details, ordinary methods, components, materials, etc. In still other instances, well-known structures, materials, or operations are not shown or described in detail to avoid obscuring aspects of various embodiments of the invention.
Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the present invention. Thus, the appearance of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures, or work characteristics may be combined in any suitable manner in one or more embodiments.
In one aspect, the present respiratory monitor allows for the detection of nitric oxide in exhaled breath, taking into account variables such as humidity, temperature, pressure, and flow rate. In general, an exhaled breath sample is received in the monitor through a sample inlet. The sample proceeds along a flow pathway and is equilibrated for humidity. The humidity-equilibrated sample proceeds along the pathway to a catalytic filter adapted to generate a known equilibrium mixture of NO and NO2 from NOx. Thereafter, the sample flows to an NO sensor configured to measure the NOx concentration in the humidity-equilibrated sample. A controller thereafter calculates the total NO in the sample. A detailed description is set out below of various embodiments of the present monitor that further illustrate the present invention.
Referring to
The flow restrictor 113 can advantageously be used to further partition the sample (as the remainder is sent through the outlet 114). That is, the flow restrictor 113 can act to create back pressure at the inlet 105 and in the user's airways that closes the user's velum (soft palate), thereby preventing nasal breath from entering the mouth and subsequently being passed through the mouthpiece. Pulling the sample portion off of the main breath can advantageously maintain the volume and flow rate of gas analyzed at a constant level. Further, siphoning off a sample of breath can reduce the power consumption and size of the device 100, enabling the device to be battery operated. That is, the smaller gas volume can be filtered, heated, and analyzed using lower amounts of power and/or smaller components than a higher gas volume would take to analyze.
The humidity equilibrators 116, 126 can include a selectively permeable membrane, such as nafion tubes (polymer-based tubes), that selectively allow water molecules to pass through the wall of said tubing, thereby equilibrating the moisture content within the tube to the moisture content external to the tube while concurrently not affecting the concentration of NO, NO2, or NOx within the tube as it passes along the length of the tube. The humidity equilibrators 116, 126 can thus be used to equilibrate humidity of the breath sample to ambient conditions. The humidity equilibrators can also be used in combination with the desiccant 106.
To enhance the accuracy of the NO detection by the microchannel reactor/sensor assembly 122, it is generally desirable to maintain a substantially constant humidity in the system. In the embodiment illustrated, ambient air is drawn into the system through the inlet 124. Further, the humidity equilibrators 116, 126 equilibrate the humidity of the breath sample to ensure that the breath sample has substantially the same humidity as the ambient air. The first humidity equilibrator 116 reduces the humidity of the sample breath only while the second humidity equilibrator 126 ensures that both the breath sample and the ambient air have a substantially equivalent controlled amount of humidity.
In some embodiments, the NO detection device also may include additional desiccant located with the mouthpiece or other areas outside of the detection box. The desiccant may be useful in helping to condition the breath gas and to avoid removing NO from the breath gas when the humidity is above acceptable limits. For example, when a specific amount of water is added to the breath gas—for example, when the atmospheric moisture of the sample increases—it may react with and thus reduce the amount of NO in the breath gas. Additional desiccant may be included to help condition the breath sample and avoid the removal of excessive NO from the sample. A pneumatic diagram of one embodiment of the NO detection device is shown in
In some embodiments, an NOx filter may be incorporated into the detection box. As shown in
In some embodiments, one or more valves may be included to balance flow from the intake and ambient air. For example, needle valves can be employed to help maintain a substantially continuous gas flow when switching from ambient to breath flow. For instance, a needle valve 502 may be located before the humidity equilibrator, as shown in
In some embodiments, the NO detection device may include one or more check valves to address changes in humidity in the reactor and sensor assembly. The valves can help avoid error readings when ambient air is not being admitted into the device; for example, when the device is turned on and off. Referring to
The microchannel reactor and sensor assembly 122 are configured to determine the total NO concentration from the breath sample gas, as shown in
The sensor and the microchannel reactor are maintained at different temperatures to provide a driving force for the NOx equilibration reactions. That is, the reactor equilibrates the NO to NO2 mixture based principally on the temperature of the reactor (which includes platinum-zeolite (PtY), and then the potential develops on the sensor element based on this equilibration of NO and NO2 changing when reacting with reference electrode (PtY) and the sensing electrode at a temperature different than the temperature of the reactor. The sensor works by measuring the potential difference between the two electrodes, and a total NOx concentration (and then NO concentration) can be calculated by comparing the potential to a calibration curve. An example of such a calibration curve is illustrated in
Details regarding a reactor and sensor is described in U.S. Pat. No. 6,764,591, titled “Potentiometric sensors comprising yttria-stabilized zirconia and measurement method of total NOx sensing without CO interference,” the entirety of which is incorporated by reference herein.
Suitable catalytic materials include, without limitation, Zeolite-Y or ZSM-5 (e.g., Zeolite Socony Mobil-5) with a surface area per mass of 425 m2/g as received. In ZSM-5, the zeolite compound is loaded with platinum ions in an ion-exchange process before being applied to the reactor portion of the reactor-sensor assembly. The structure enables increased loading of platinum clusters onto the zeolite material. In one embodiment using ZSM-5, the catalytic material may contain approximately 1-4% μm platinum in zeolite. Although platinum is described as an example, alternative catalysts could be used and dispersed in a zeolite or other high surface area structures.
Referring to
As show in
Referring to
As shown in
Advantageously, by having the microchannel reactor and sensor 122 assembly set up as a series of plates as describe herein, the ratio of surface area of PtY exposed to the volume of air sample is maximized. Further, using plates can allow the microchannel reactor/sensor assembly 122 to be relatively small, allowing the device 100 to be more easily portable, and reducing the energy needed to heat the air sample. In other embodiments (not shown), the microchannel reactor and sensor 122 assembly can be fabricated using other techniques to further miniaturize the assembly. For example, various material deposition (additive) and removal (subtractive) processes may be employed to create microchannel reactor and sensor assemblies having even smaller dimensions. The assemblies can be built up layer by layer using chemical vapor deposition (CVD), physical vapor deposition (PVD), electrodeposition, electroless deposition, or the like. In some embodiments, voids for air flow, such as those shown in
Referring to
The device 100 can be configured to precisely control the important variables, such as humidity, temperature, pressure, and flow rate. For example, the humidity can be controlled using the first and second humidity sensors 110, 119. The first humidity sensor 110 can detect the amount of humidity that is coming into the device 100 from the patient's breath through the mouthpiece 102. The second humidity sensor 119 can detect the amount of humidity once the breath transverses the humidity control system into the microchannel reactor/sensor 122. If the humidity level at the second sensor 119 is equal to or greater than that at the first sensor 110, this may be indicative of a fault in the system. Accordingly, a controller can signal an error. The humidity at the second sensor 119 should be substantially equal to ambient conditions and controlled tightly to the ambient humidity level, such as to have a humidity within 2% of ambient. This control ensures that the humidity level that is going into the microchannel reactor sensor assembly is substantially constant during the duration of a measurement.
Further, the temperature difference of the catalytic converter and the sensor can be controlled by the RTD or RTDs to be within about 100-300 degrees Celsius, such as about 200 degrees Celsius. Precise control of this temperature difference is important in some embodiments, as the higher the temperature difference, the greater the signal. In use, the catalytic converter should operate above 200 degrees Celsius in order to maintain reaction efficiency while the sensor should operate in excess of 350 degrees Celsius to activate oxygen conduction within the sensor electrolyte material. Further, in some embodiments, temperatures above 950 degrees Celsius at the NO sensor could be too high for the device to function properly while temperatures below 200 degrees Celsius at the reactive filter could be too low for the catalytic reactive filter to function efficiently. In one embodiment, the desired temperature difference is achieved by ensuring that the electronics keep the temperature of the reactive filter and the temperature of the sensor nominally at 250 degrees Celsius and 550 degrees Celsius, respectively.
The flow sensor 108 and pressure sensor 112 can be used to trigger the 3-way control valve 118 to toggle and pull from the breath sample line rather than the ambient line, thereby feeding the breath sample over the microchannel reactor/sensor assembly to perform the NOx measurement. In some embodiments, the target flow rate is 3 L/min (+/−10%). Likewise, pressure sensors can look for a pressure of 5 to 20 cm of H2O. If either of the flow rate or the pressure range is not met, the 3-way control valve 118 can be configured not to toggle, and as such, the NO sensor will not measure NO in the patient's breath. In some embodiments, the pressure and flow sensors 108, 112 can also be used to provide feedback to the user regarding the pressure and/or flow so as to help the user provide the necessary pressure and/or flow for activation of the NO measurement. Further, in some embodiments, the user is required to meet both the pressure and flow rate goals continuously for a total of less than 15 seconds, such as approximately 10 seconds, in order to obtain the NO reading.
In some embodiments, by controlling all of these variables, the accuracy of the resulting NO reading can be within +/−10 ppb, such as within +/−7 ppb or within +/−3 ppb.
Referring to
In some embodiments, the device 100 is calibrated using electronics coupled to the microchannel reactor and sensor. To do so, the heating parameters for each reactive filter and sensor assembly can be uploaded to the device when the micro-channel reactive filter and sensor assembly is plugged into the device. The microchannel reactive filter and sensor assembly (MCRS) can also provide the calibration curve parameters to the device. This is how the device interprets whether a measured potential from the sensor is equal to a specific NO concentration. A sample calibration curve is shown in
The detection system 100 can be a flow-through device in that air (either from the ambient through inlet 124 or from the breath at mouthpiece 102) can continuously flow into and out of the system. That is, the amount of air into and out of the system at any one time can be controlled. Having a controlled and continuous flow of ambient air through the device before and after the user's breath can advantageously set a reliable baseline for NO measurement. Further, by providing analysis of the breath via continuous airflow (i.e., without storing the breath), the NO reading can be provided quickly and efficiently. For example, the system can provide the NO reading in less than 15 seconds from when the user begins to breath into the device.
The flow rate through the mouthpiece can be regulated to 3 L/min (+/−10%). The flow through the catalytic converter and NO sensor can be in the 0.01 to 1 L/min range, such as 0.2 L/min. The power needed to heat the MCR can be 2-9 Watts. The mass of the reactive filter (catalytic converter) can be within 2-200 grams. The external dimensions of the microchannel reactive filter and sensor assembly in this embodiment are nominally 0.75 inch×1.25 inch×0.5 inch. The variation for the temperate at the converter can be less than +/−2 degrees Celsius. The efficiency of the converter can be >90% to ensure proper performance of the sensor.
As described above, pulmonary function tests typically require different machines for conducting different tests. For example, the large delta between the breath flow rates for spirometry and FeNO measurements has previously prevented use of a single mechanism to make the measurements. In the embodiment illustrated below, multiple markers, such as spirometry and eNO tests, can be measured and tracked in a single device mediated by airflow-restriction mechanism. Other pulmonary function tests or gas sensors may be employed in the device illustrated.
In one embodiment, a monitoring device is contained in a housing that contains an inlet section, a measuring section and a flow detection component. In addition, the device contains an adjustable airflow restriction component and at least one gas detection sensor. The inlet section receives a gaseous sample from a subject, e.g., a subject, or source, that expels air into the inlet section, which then proceeds downstream into the device according to variable restrictions that alter the speed and path of the gaseous sample expelled from a subject into the device. In the embodiment illustrated, an inlet section is positioned in the housing and configured to receive a gaseous sample. A measuring section is positioned adjacent to the inlet section and connected via a hole in the inlet section. A flow detection component is positioned in the inlet section and configured to measure the flow rate of a gaseous sample entering the inlet section. Positioned upstream of the flow detection component is an airflow restriction component. An adjustable partition can also be positioned downstream of the flow detection component, which can be adjusted to further direct and restrict airflow. At least one gas detection sensor is positioned in the measuring section.
As indicated above, the lung-function monitoring device comprises two sections for collecting and sensing a gaseous sample from subjects. An inlet section is composed of an inlet port or channel having an orifice at one end that extends axially along an airflow path to the opposite end, which incorporates an airflow restriction component, such as a shutter-controlled aperture. A disposable or easy-to-sterilize mouthpiece can be adapted to the orifice opening to allow for directing airflow into the inlet section. When performing a spirometry test, for example, a user blows air into the device via a mouthpiece to an inlet port where a gaseous sample can flow through a flow detection component, such as an impeller-based flow meter, and exit the inlet section via an opposite opening that exits the device. Conversely, when performing eNO test, a user steadily exhales breath into the inlet section with the airflow restriction component in a restricted position, which consequently re-routes the gaseous sample to the eNO detector contained in the sensing section. To further close off an airflow out of the device, a movable partition on the back of the housing can be moved to a closed position during this test to further retain and re-route the gaseous sample through the hole and into the measuring section. At least one gas sensor, e.g., such as the NO sensor described above, is placed along a sensing compartment.
To further illustrate the invention, reference is made to the drawings that are directed to one embodiment of the present invention. Referring to
Referring more specifically to
Referring to
Referring to
In the embodiment illustrated, the impeller assembly of the flow meter requires a certain amount of air flowing into the device to cause the impeller assembly to spin. At a very low flow rate, the impeller will not spin, or will spin erratically. When a subject forcefully expels air into the device for certain measurements, e.g., a pulmonary function spirometry test, a gaseous sample flows through the impeller, causing it to rotate. In a typical spirometry test, the airflow can range from 100 to 700 LPM. The air then exits at the opening end of the shutter-controlled aperture. The amount and speed of air passing through the impeller can then be detected by sensing means along the impeller assembly. In one embodiment of the present invention, the measured lung function parameters from the flow meter can be converted to signals and transmitted to a microcontroller integrated with the monitoring device.
Again referring to
Referring more specifically to
When the flow shutter is fully open in response to manual control or to an electrical signal during a spirometry test, which requires a user to exhale forcefully, the open shutter allows the free flow of air entering the inlet section. Meanwhile, a flow rate can be measured by a flow meter.
As described, the shutter-controlled mechanism of the present lung-function monitoring device allows measurement of gaseous samples requiring selected flow rates. For example, measurement of eNO concentration requires a steady flow of air, for example, of 3 to 5 LPM over a period of about 10 seconds. To conduct this test, the aperture of the shutter assembly is adjusted manually or electronically to achieve a predetermined flow rate. The closed exit of the inlet section results in redirecting the inflow of exhaled breath to the contiguous sensing section coupled with at least one NO sensor contained in the sensing section to measure the level of NO in exhaled breath. As illustrated in
By way of illustration, in one embodiment of the invention, the device can be constructed to make three respiratory measurements, e.g., (1) a spirometry test, which includes common tests such as PEF and FEV1 wherein the user exhales forcefully into the device during a short time at rates ranging from 100 to 700 LPM, (2) a fractional exhaled nitric oxide test (FeNO) wherein the user exhales at a controlled rate of approximately 3 LPM over a period of approximately 10 seconds, and (3) a respiratory rate test. A large diaphragm shutter upstream of an optical-impeller based flow meter allows for the measurement of large, short duration flows of up to about 700 LPM when the leaf shutter is in the open position and air flow is substantially unrestricted through the device, e.g., the adjustable partition is in the open position, allowing for the free flow of the spirometry test to be exhausted out of the device. When the shutter is in its restricted position, air flow through the device is limited to no more than about 5 LPM, allowing for the NO test that requires the slow, steady exhalation of breath. In the restricted position, the air flows to the nitric oxide sensor, such as a solid-state nitric oxide sensor. In one embodiment, the restricted flow can be siphoned off, for example by a pump that siphons off the sample through the impeller shell hole, and delivered to the NO sensor. The pump can also be used to purge the device. The respiratory rate can be measured using an accelerometer that measures chest wall movements that correlate to breaths. In one embodiment, an accelerometer for measuring respirations (e.g., breaths per minute) can be coupled to the user's torso. Measurements from the accelerometer can be transmitted to the monitoring device of the present invention by wire, or wirelessly.
In addition to the above, in one embodiment the device is constructed to perform two other peripheral measurements: (1) pulse, and (2) pulse oximetry. These blood flow measurements can be made using optical sensors per standard methods.
With the above-described capabilities, the device can measure at least four markers that are of importance to asthma patients and doctors. Additional features and embodiments are described below.
As illustrated, a user generally exhales into the device through a mouthpiece. Any suitable mouthpiece may be employed in the practice of the invention described herein. However, it is advantageous to employ a mouthpiece that allows a user to inhale outside air through the mouthpiece, and exhale through the mouthpiece and into the device through a path separate from the path of inhaled air. It is further advantageous to filter the inhaled or exhaled air with one or more filtering media. One embodiment of such a mouthpiece is illustrated below.
Referring to
As described above, the illustrated mouthpiece can contain one or more filters or filtering media. For example, referring more specifically to
The filters or filtering media may be of any appropriate kind. By way of illustration, filters and filtering media can be adopted for screening out gases of interest, including NOx, CO, CO2, NH3, O2, H2O, etc. Examples of filtering media include activated alumina, Sofno-Fil, Sofno-Lime, silica, activated zeolite structures, and the like. Paper filters may be of any appropriate type for the intended function, for example, polypropylene, paper, cotton, or other fabric depending on the desired function.
The mouthpiece housing can be composed of any suitable materials. For example, the materials chosen should not interfere with the flow of the gases through the device or the filter materials. One such suitable material is polyethylene terephthalate (PET). The mouthpiece can be a single use, disposable component that can be sanitized prior to use or packaging, or easily sanitizable and reusable.
The described mouthpiece has numerous advantages. It can reduce the maintenance of monitors by moving the consumable filter media to a single use, disposable component. Or, in another embodiment, where the mouthpiece is reusable, filter media may be replaced or recharged as needed. This can reduce the need for monitor servicing, e.g., for the purpose of changing filter media or valves. This improves the cost efficiency of the monitors. Safety is increased because some breathing devices require the user to inhale through the device, potentially allowing bacteria or fungi from the device to enter the user. The described mouthpiece can also filter species that are detrimental to breath analyses.
In a particularly preferred device, the mouthpiece will operate with greater than fifty percent efficiency in the removal of specific species. For example, removal of moisture should reduce exhaled breath relative humidity to between 5 to 70%. Ingress and egress flow rates of between 25 to 300 sccm are desirable. Operating conditions should be ambient temperatures between 10 degrees Celsius to 45 degrees Celsius and relative humidity of between 5% to 99%.
In another embodiment of the present invention, pulmonary function, and other related tests, can be enhanced by incorporating a microcontroller. For example, a user can enter his or her data into the microcontroller, execute programs and receive the transmitted signals from integrated flow meter and NO sensor. The microcontroller can further include information storage means for storing entered parameters and received data.
In another embodiment, one or more gas sensors can be configured to measure clinically relevant-biomarkers, e.g., H2, CO, or O2 can be integrated with the present lung-function measuring device. Other sensing methods, e.g., electrochemical, acoustic, calorimetric, optical, or biological sensing methods can be incorporated for detecting gas molecules. For example, as described above, optical sensors (e.g., pulse oximetry) can be incorporated for measuring blood flow characteristics.
In another embodiment, the portable microcontroller can integrate with selected wired or wireless networks, e.g., Wi-Fi, Bluetooth, or USB to transmit and store data at remote locations. GPS can also be integrated to provide user location. For example, testing data can be automatically forwarded to a physician for monitoring and analysis.
In another embodiment, the device can obtain the user's location and local weather conditions, including air quality, and subsequently record and transmit this data. In a particularly preferred embodiment, fractionally exhaled nitric oxide concentration (FENO score) can be tracked and presented alongside tracking for other spirometry values such as FEV1, FEV6, PEV, FVC, TLC, and SVC, and alongside other environmental factors such as outside air temperature, weather conditions, wind speed, wind direction, barometer values, barometer trends, pollen count, air quality, ground level ozone, dew point, and humidity.
As a further illustration, the device 100 can be used with a data storage and information system to provide users and caregivers with asthma-related information. For example, referring to
In some embodiments, the device can be configured to gather environmental data using a sensor built into the device. In other embodiments, the device's location can be determined by GPS or cellular triangulation, or Wi-Fi signal triangulation or other system sensor or a combination in whole or part of such systems and then querying a national and accepted data source for the above mentioned environmental parameters.
In other embodiments, the devices described herein can be used with a subscription service. For example, a physician can buy a subscription for so many uses of the device, then the physician will be granted access to the “ecosystem” database that can provide specific user results including but not limited to historical trends, local trends, regional trends, notifications may be such things as appointment reminders, or a notice of high pollen count within a nearby region that mayor may not correspond to particular NO reading, etc. The subscription service would also provide the user or physician the ability to record and or maintain a symptom diary that would be tracked along with exhaled nitric oxide measurements, and or any additional clinical or non-clinical data of interest to the user, physician, or other party.
As described above, there is an abundance of relevant medical and environmental parameters that bear on monitoring and evaluating an individual's respiratory functions. Relevant parameters also include an individual's activity and behavior parameters. The ability to collect, store, and analyze such parameters can be of tremendous benefit to patients, caregivers and healthcare professionals. With devices, such as those described herein, relevant parameters can be communicated to a secure computer network data system that collects, stores and analyzes such data. Moreover, once such data is collected and analyzed, it can be tracked and can be accessed via a customizable computer graphic interface. Consequently, the ability to simultaneously view such data in a customizable graphical user interface allows the plethora of available data to quicken the evaluation by healthcare professionals and individuals, such as patients.
Relevant medical parameters include, in addition to exhaled nitric oxide measurements, values obtained for other medical parameters of interest, such as nasal nitric oxide, exhaled CO and CO2 levels, exhaled acetone, exhaled ketones, interleukin counts PEF, FEV1, FEV6, PEV, FVC, TLC, and SVC, blood eosinophil counts, blood oxidation levels, pulse oximetry, weight, height, BMI, and the like.
Environmental parameters include values such as ambient NO, air quality, airborne particle count temperature, dew point, wind speed, wind direction, pollen count, pollen blooms, smog, and the like. An individual's activity and behavior patterns include exercise and medication therapy adherence and the like.
As indicated, relevant medical and environmental data can be communicated, such as by uploading, to a computer network data system. Programs for analyzing, tracking and displaying the data can be computer based, cloud based or a combination. Access can be accomplished by any suitable computerized device that can display the information desired, such as desktops, laptops, tablets, mobile devices, and an appropriate respiratory monitor, such as those described herein, having a suitable microcontroller and graphical user interface display with access to the network that enable data communication between the device and the network such that data can be displayed on the accessing device,
A computer implemented method for collection, storage, analysis, and facilitating access to the medical data and medically relevant data such as environmental parameters or patient behavioral data can be presented by a number of methods including but not limited to: graphs, plots, maps, pictures and tables for the purpose of providing environmental and behavioral context (potential correlation) to medical parameters of interest.
Networked diagnostic devices, such as those described herein, can send data to the networked system that includes date, time, location, user identification number, and clinical parameters such as exhaled nitric oxide concentration, and device specific information regarding device performance, etc. Networked diagnostic devices can also receive data from the networked system that includes active user identification numbers, and software update information, etc.
In a preferred embodiment, a network accessed graphical user interface is employed that will be displayed during access to the network that is capable of displaying queried data in the form of graphs, charts, maps, pictures, and tables in a specific format based on the user's preference and access level. Further the user interface will be capable of determining and maintaining security based on the user's level of access, but always transmitting data in such a manner that it uses appropriate security measures, such as encoding, encryption, pass-key access, etc.
The network accessed graphical user interface may be primarily used to display a single patient profile that would include that specific patient's specified medical parameter historical data shown on a trend chart. Such trend charts can display a single, or a plurality of medical parameters using the equivalent time based scale and such that the axis are consistent or matching orientations of goodness. For example FEV1 can be displayed as a percentage of 100 where 100% is good. FeNO can be shown on scale of 5-300 where low numbers are good. The FeNO score can be oriented such that the lowest score (5 ppb) is oriented at the top (up). Additional parameters selected by the user for display can be presented in similar fashion
In addition, at the preference of a user, medical parameter trends can be simultaneously displayed with environmental data trended by the location preference chosen by the user. For example, a patient and their doctor's office are often not co-located, thus when a health care professional (HCP) is reviewing a patient's profile, the HCP may elect to view FeNO scores simultaneously with the air quality historical data for the HCP's office, or it maybe displayed with the air quality historical data from the patient's home address, city, zip code, or other means of geo-locating. Moreover, the graphical user interface can display historical data trends that may include special notes regarding specific data points. For example, in the context of FeNO measurements and geo-location, it can be noted where a particular patient may have traveled in between or during a particular evaluation. As such, an environment not typically listed (HCP office, home, work, etc.) can be noted and taken into account.
The NO detection device of the present invention may include different elements sized and configured to allow for further manufacturing efficiencies and enhanced portability. Exhaled breath from a user enters the detection device via a sample inlet and through a flow pathway within the detection device. In some embodiments, the flow pathway includes a reactor and sensor assembly that comprises a reactor portion with a catalytic filter, a sensor portion with a plurality of sensor pads, and a unitary heating element with a resistive temperature device. The reactor portion receives the humidity equilibrated breath sample and generates a known equilibrium mixture of NO and NO2 from NOx. The sensor portion includes a sensor that measures the NOx concentration in the sample, and a controller calculates the total NO in the sample based on the measured NOx concentration and the known equilibrium.
In one embodiment, the reactor and sensor portions of the assembly may be placed in separate gas chambers that are connected by one or more gas channels. The heating element is placed between the reactor and sensor portions. The heating element distributes heat to both portions of the assembly. In a preferred embodiment, the heating element includes a single heater with heat separation or conduction media between the reactor and sensor portions. The configuration allows the reactor and sensor portions of the assembly to be maintained at different temperatures using a single heater and resistive temperature device.
Advantageously, the inclusion of a unitary heating element may reduce the power consumption required to achieve the desired operating temperatures and remain stable. Such a reduction of power may be beneficial from a usability perspective because the device may manage the current power remaining and allocate appropriately. The design may further reduce the overall size of the NO detection device. This architecture may also allow for an enhanced sensing device with a compact body that is suitable for a variety of uses, including without limitation, a compact hand-held device. As will be described below, some features of the heater and resistive-temperature device may also allow for manufacturing efficiencies and reduce the number of electrical connections required for the device.
The reactor-sensor architecture may be well suited for use in a personal portable device monitor that performs gas measurements for NO, for which compact size, fast warm-up times, and fast stabilization times are particularly important. The device may allow the measurement of NO content of a gas using a compact reactor and sensor assembly in a compact, portable, battery powered package that can be used or breath or other gas analysis. Given the efficiency of the device, the design may also increase the resolution of breath sampling. The assembly is well suited for performing exhaled nitric oxide measurements and analysis that are beneficial for asthmatics to perform on a frequent basis to monitor airway inflammation. In addition, the reactor-sensor assembly may used for a personal portable device that performs gas measurements for air born molecules when adapted with additional or alternative sensors, such as those used to detect CO, acetone, NO2, NOx, CO2, ammonia, and others substances.
In some embodiments, the reactor portion of the reactor-sensor assembly is coated with a catalytic material that is used to precondition the gas fluidly transferred to the sensor portion of the reactor-sensor assembly. The catalytic material should have a high surface area that promotes the chemi-adsorption of the gas molecules so that the gas molecules can be reacted with high efficiency before continuing in the fluid flow path. Suitable catalytic materials include, without limitation, Zeolite-Y or ZSM-5 (e.g., Zeolite Socony Mobil-5) with a surface area per mass of 425 m2/g as received. In one embodiment using ZSM-5, the catalytic material may contain approximately 1-4% μm platinum in zeolite. Although platinum is described as an example, alternative catalysts could be used and dispersed in a zeolite or other high surface area structures.
The reactor portion is maintained at a condition that provides a consistent catalytic efficiency. The conversion efficiency is dependent on variables such as the flow rate, the nominal surface area of catalyst, the depth of the catalytic coating on the surface, the temperature of the catalyst, and humidity. In one embodiment, the reactor-sensor assembly may operate with a given flow rate range from 5 to 8 mL/min through the assembly, and the reactor portion is maintained at a constant temperature within the temperature range of 250 to 700° C., typically 280 to 350° C. In another embodiment, the reactor-sensor assembly uses a flow rate range of 7 to 50 mL/min and a temperature range from 275 to 350° C. In a preferred embodiment, the reactor portion operates at a well-maintained temperature of nominally 280+/−50° C. In an alternative embodiment, the reactor portion may have an additional heater and resistive thermal device (RTD) to monitor temperature that will be controlled and monitored by a central computing controller chip that will control the components to target temperatures.
The reactor portion of the reactor-sensor assembly will be heated to a different temperature than the sensor portion to provide a driving force for the NOx equilibration reaction. In some embodiments, the sensor portion will be maintained at a temperature between 300 and 900° C. In other embodiments, the sensor portion is heated to a target temperature of between 350 and 500° C. In a preferred embodiment, the sensor portion operates at a well-controlled temperature of nominally 450+/−50° C.
Referring to
The housing defines two chambers divided by the sensor substrate. One chamber includes the catalyst layer, and the other chamber includes the sensor layer. Each of the chambers has an inlet and outlet, and air is forced through and then outside of the unit after exiting the sensor chamber. In some embodiments, the catalyst (reactor) chamber and the sensor chamber are connected by one or more fluid conduits. Here, one or more intermediate cooling tubes (not shown), such as a Viton tube, may be used to connect to the catalyst and sensor chambers. The cooling tube may be placed outside the unit to connect the outlet of the catalyst chamber to the inlet of the sensor chamber. Other structures (e.g., pipes, tubing, or connecting structures) that are capable of fluidly delivering gas may be used.
The heating element can 605 advantageously provide preferred heat distribution to the sensor and catalyst layers. The reactor and sensor portions of the assembly are maintained at different temperatures, and advantageously, the reactor-sensor assembly can be designed to allow for precise detection and control of the heat differences in the catalyst and sensor layers of the assembly. In addition, the device can be configured to control other important variables such as humidity, pressure, and flow rate. It will be appreciated that a number of variables, such as the temperatures and temperature differences in the catalyst and sensor chambers, may be controlled by adjusting the materials or the amount of materials applied to the assembly. As a non-limiting example, the heat distribution to the different chambers may be modified by the use of an insulator material with different heat transfer properties. The heat distribution can also be affected by changes in the amount of catalyst mass present, relative to the mass of the sensor. In addition to material selection and amounts, heat distribution from the heating element may also be affected by the dimensions of the chambers. For example, increasing the available volume of one of the chambers through which a gas sample flows may increase the temperature difference between the chambers. The temperatures may also be adjusted by modifying the heat supplied to the assembly through a heat trace, for example.
The sensor may be secured to the sensor substrate in any suitable way. As an example, the sensor may be placed on the sensor substrate above the thermal insulator, which helps to support the sensor. In this embodiment, the insulator may have a thermal conductivity of approximately 0.1 W/mK, a thickness of approximately 0.3 mm, and thermal resistance of approximately 3 m2K/W. The sensor and catalyst may be heated to temperatures of approximately 400° C. and 200° C., respectively, using a power consumption of approximately 4 W.
In yet other embodiments, the sensor may be suspended from an upper surface of the sensor substrate using welding wires. In this example, the sensor and catalyst may be heated to temperatures of over 400° C. and slightly under 200° C., respectively, using a power consumption of approximately 4 W.
Alternatively, the sensor may be secured to the sensor substrate using bonding wires. That is, the thermal insulator is secured to the sensor substrate using inorganic adhesive. The heating layer is placed above the insulator. The sensor is positioned above the heating layer and secured to the substrate using bonding wires. Optimally, the space separating the inner surface of the upper metal housing and the sensor substrate should be sealed using an elastic material, as should the space separating the inner surface of the lower metal housing and the catalyst.
In a preferred embodiment, the housing (e.g., a main resin enclosure) may measure approximately 45 mm in length, 25 mm in width, and 20 mm in height with a catalyst measuring approximately 11 mm×7 mm×3 mm. In another embodiment, the size of the enclosure may be increased to approximately 30 mm×50 mm×100 mm, depending on assembling and operation variables such as: ease of assembly, requirements for the surface temperature of the enclosure, desired heat exchange parameters, and size of the catalyst and its conversion efficiency.
A further advantage of the present invention is a reduction in the number of electrical connections between the reactor-sensor assembly and the controller. The sensor used in the reactor-sensor assemblies described in the present invention may be constructed to include different types of electrical connections on either side of the sensor/heater assembly. In some embodiments, the reactor-sensor assembly has a minimum of six electrical connections to the controller for: the reactor-sensor heater (+), reactor-sensor heater (−), reactor-sensor resistive temperature device (+), reactor-sensor resistive temperature device (−), sensor signal (+), and sensor signal (−). These electrical connections are made to minimize electrical interference and to reduce the amount of heat transferred out of the reactor-sensor assembly.
Referring to
In an alternative embodiment of the present invention, the electrical connections are located on a single face of a sensor substrate. Referring to
Because this structure uses weldments on only the sensor-side face, it reduces the strain that might otherwise change the electrical signals in the assembly. The use of thru-holes and pins may also simply manufacturing in that it requires electrical connections and weldments on only one side of the heating element. The electrical connections may be created by wire bonding with Au wire or other welding methods known in the art for joining metal components.
In another embodiment, the reactor-sensor assembly may be housed, at least in part, within a ceramic package and positioned on a printed circuit board. The sensor is fixed and electronically connected to the package, with a muffler-like catalyst unit placed below the sensor via one or more insulation layers. In this embodiment, the reactor-sensor assembly utilizes the ceramic package and related technologies to save mass and power consumption, particularly in situations of low temperature around the device.
Referring to
A catalyst unit 706 is placed below the sensor via the insulator 707. The catalyst unit may be sized and constructed to fit within the inner surfaces of the base housing (as shown in
Referring to the assembled unit shown in
A cross-section of an assembled reactor-sensor assembly integrated with a ceramic package is illustrated in
In a preferred embodiment, the reactor-sensor assembly may measure approximately 25 mm in length, 34 mm in width, and 20 mm in height with a catalyst measuring approximately 5 mm×3 mm×2 mm. The enclosure may be sized to be larger or smaller, however, depending on assembling and operation variables such as, without limitation, ease of assembly, requirements for the surface temperature of the enclosure, internal heat exchange parameters, and size of the catalyst and its conversion efficiency.
Thermal Zones within the Reactor-Sensor Assembly
In one embodiment, a housing includes a series of internal surfaces formed by for lid-shaped surfaces, for example, nested within another and placed over the bottom of the housing. The internal surfaces create an elongated flow path and zones through which breath gas may flow. As illustrated in
Referring to
The breath gas then flows through a catalyst zone where it is allowed to react with the catalyst. It is then cooled as the gas flows through a cooling zone, after which the breath gas contacts the sensor in sensor zone. In a preferred embodiment, the sensor may be heated to approximately 400° C., while the temperature of a Pt—Y catalyst may be maintained at approximately 300° C. with the aid of the heat exchange occurring in the cooling zone.
It is contemplated that the temperature differences in the zones of the reactor-sensor assembly, including the particular temperatures at which the sensor and catalyst zones are maintained, may be adjusted in one or more ways to optimize and/or control heat flow within the system. For example, the materials used, including the material selected for the insulator, may be modified to change the heat transfer properties within the system. The dimensions of the metal housing, such as the length, width, and height, may be modified to adjust the surface area of the internal surfaces and the volumes of the zones or chambers through which breath gas flows. The distances of the layers from the heating element may also be adjusted; for example, by changing one or more thicknesses of the layers or the distances from the heater location. The amount of catalyst material applied relative to the amount of sensor material present may also be adjusted to change the temperatures (or the temperature differentials) in the system. The distances of the flow paths may also affect the heat exchange properties within the assembly.
In another embodiment, a reactor-sensor assembly may include yet other configurations to allow for additional treatment of the gas flowing through the assembly. In one embodiment, a reactor-sensor assembly may include a reactor chamber, sensor chamber, a heating element between the reactor and sensor chambers, and one or more external gas conduits connecting the two chambers. A sensor substrate, for example, an alumina substrate, divides the chambers. A catalyst filter (PtY, for example) is positioned near the inlet of the reactor chamber to allow an extended flow-path for the gas sample after it has contacted the catalyst filter. The flow path of the gas sample after it has contacted the catalyst filter in this example is extended, as compared with an assembly where the catalyst filter is placed in or near the center of the reactor chamber. The extended flow path allows for cooling of the inlet gas sample before it reaches the sensor chamber.
Similarly, in some embodiments, a sensor layer may be positioned in the sensor chamber near the outlet area of the gas sample. The flow path of the gas samples before it contacts the sensor layer is also extended, as compared with an assembly where the sensor layer is positioned at or near the center of the sensor chamber. This extended flow path allows for additional cooling of the as sample in the reactor chamber.
In yet another embodiment of the present invention, the reactor-sensor assembly may be configured to allow for substantially linear gas flow through the assembly. Referring to
A breath gas sample flows substantially linearly across the substrate, as shown in flow path 905. Breath gas flowing into the reactor-sensor assembly is passed through an initial pre-treatment area where it is heated before it is allowed to react with the catalyst. The breath gas then flows through a catalyst zone where it may interact with the catalyst. A segment of the substrate then provides a cooling zone where the breath gas is allowed to cool. The breath gas then flows through the sensor zone where it contacts the sensor.
A housing (not shown) surrounds the assembly. The housing may be made of various materials known in the art that allow for mechanical strength, ease of use, and effective maintenance of target temperatures within the reactor-sensor assembly. Suitable materials include, without limitation, stainless steel, alumina, plastic polyphenyline sulfide (PPS), ceramic, and beryllium oxide.
The reactor-sensor assemblies described above are designed to allow the maintenance of different temperatures in each of the zones. To that end, the heating element may be designed to distribute different amounts of heat to each of the zones. Moreover, the heating element may be modified to achieve target temperatures within the different assembly zones. For example, the temperatures or the temperature differentials in each of the zones may be further modified by changing the number of coils or loops in the heater trace. The temperatures may also be changed by varying the thickness or the width of the trace. The location of the catalyst and sensor on the substrate may also affect the temperatures in the various zones. For example, placing the catalyst and sensor farther away from each other allows for additional cooling of breath gas after it reacts with the catalyst and before it contacts the sensor.
The component shapes, dimensions, and geometries described above for the reactor-sensor assemblies are provided as examples. The particular flow paths, shapes, forms, dimensions, and geometries described above may be modified to achieve the desired heat transfer properties or other performance properties within the reactor-sensor assemblies or as desired to improve manufacturing and operation. The heat transfer properties may be changed by modifying factors known in the art to affect heat transfer, including without limitation: the materials selected for use; the shape and dimensions of the path through which the gas sample flows; the shape and/or size of the of the metal housing; the shape and/or size of chambers through which gas flows; the surface areas of the internal surfaces contacting the gas sample; the volumes of the zones or chambers through which breath gas flows; the flow rate of gas entering the device; and the distances of the layers from the heating element.
As for additional details pertinent to the present invention, materials and manufacturing techniques may be employed as within the level of those with skill in the relevant art. The same may hold true with respect to method-based aspects of the invention in terms of additional acts commonly or logically employed. Also, it is contemplated that any optional feature of the inventive variations described may be set forth and claimed independently, or in combination with anyone or more of the features described herein. The breadth of the present invention is not to be limited by the subject specification, but rather only by the plain meaning of the claim terms employed.
This disclosure is sufficient to enable one of ordinary skill in the art to practice the invention, and provides the best mode of practicing the invention presently contemplated by the inventors. While a full and complete disclosure is made of specific embodiments of this invention, the invention is not limited by the exact construction, dimensional relationships, and operation shown and described. Various modifications, alternative constructions, design options, changes and equivalents will be readily apparent to those skilled in the art and may be employed, as suitable, without departing from the spirit and scope of the invention. Such changes might involve alternative materials, components, structural arrangements, sizes, shapes, forms, functions, operational features and the like.
This application is a continuation-in-part of U.S. patent application Ser. No. 14/495,853 filed on Sep. 24, 2014, which claims priority from and is related to U.S. Provisional Application No. 61/949,871, filed Mar. 7, 2014, and U.S. Provisional Application No. 61/955,192, filed Mar. 18, 2014. These prior applications, including the entire written descriptions and drawing figures, are hereby incorporated into the present application by reference in their entirety.
| Number | Date | Country | |
|---|---|---|---|
| 61949871 | Mar 2014 | US | |
| 61955192 | Mar 2014 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 14495853 | Sep 2014 | US |
| Child | 15213224 | US |
