Patent Application
20240298920
The present disclosure relates in general to a device and a system for monitoring a concentration of volatile breathing compounds, in particular but not limited to fractional exhaled nitric oxide (FeNO) and/or exhaled carbon monoxide (eCO), in respiratory gases of patients. A device is provided by which patients can be examined for potential presence of inflammatory diseases in the lungs.
The content and concentration of certain respiratory gases of patients (i.e., their exhaled breath) can reveal physiological information about a person, such as a potential presence of inflammatory diseases in the lungs. Several components of the respiratory gases are either produced or altered by the cells of the lungs and the respiratory tract. The physiological information that can be examined may for instance be used to diagnose pathological conditions and/or the effect of a particular treatment. Several volatile breathing compounds exist that may and/or have been shown to reveal physiological information. Two of these indicative components are nitric oxide (NO) and carbon monoxide (CO) even though many other components may convey indications of other respiratory conditions.
For purposes of summarizing the disclosure and the advantages achieved over the prior art, certain objects and advantages of the disclosure are described herein. Not all such objects or advantages may be achieved in any particular embodiment. Thus, for example, those skilled in the art will recognize that the invention may be embodied or carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other objects or advantages as may be taught or suggested herein.
All of these implementations are intended to be within the scope of the invention herein disclosed. These and other implementations will become readily apparent to those skilled in the art from the following detailed description of the preferred implementations having reference to the attached figures.
In one embodiment, a device configured for monitoring a concentration of at least one volatile breathing compound in respiratory gases of patients can include: a patient respiratory gas interface including a mouthpiece for the patient to blow a respiratory gas into; a connector adapted to couple the patient respiratory gas interface to a gas conduit, the gas conduit leading the respiratory gas through a flow meter and a valve, wherein the flow meter configured to measure a predefined first flux level of a patient respiratory gas flux, wherein the gas conduit is configured to further lead the patient respiratory gas through an inlet into an intermediate gas storage having a winding inner volume, wherein the intermediate gas storage is open-ended via an exhaust outlet to let patient respiratory gas exhausts in excess of a volume of the intermediate gas storage out of the same in response to the flow meter sensing an expiration of the patient respiratory gas flux; and a pump configured to draw the patient respiratory gas with a predefined second flux level in a reverse direction out of a sampling gas outlet of the intermediate gas storage and into a gas sampling line, wherein exhaled concentrations of the at least one volatile breathing compound are determined by corresponding at least one volatile breathing compound detector.
In some embodiments, the pump is arranged downstream of the at least one volatile breathing detector when the patient respiratory gas flows in the reverse direction. In some embodiments, the volatile breathing compound includes at least one of fractional exhaled nitric oxide (FeNO), exhaled carbon monoxide (eCO), hydrogen (H2), hydrogen sulfide, (H2S) and ammonia (NH3).
In some embodiments, the corresponding at least one breathing compound detector is at least one of an NO detector, a CO detector, an H2 detector, a H2S detector, and an NH3 detector. In some embodiments, the flow meter includes a feedback display unit configured to display to the patient an actual exhaled patient respiratory gas flux in relation to the predefined first flux level while the patient is exhaling.
In some embodiments, the flow meter includes a differential pressure gauge. In some embodiments, the predefined first flux of respiratory gases is between 30-70 ml/s, between 40-60 ml/s, or at least 50 ml/s.
In some embodiments, the winding inner volume of the intermediate gas storage includes rounded corners. In some embodiments, the patient respiratory gas is drawn in the reverse direction through the gas sampling line with a predefined second flux level of 40-80 ml/min, of 50-70 ml/min, or of 60 ml/min.
In some embodiments, the intermediate gas storage has a patient respiratory gas intake volume of approximately 40-80 ml, approximately 55-65 ml, or approximately 60 ml. In some embodiments, the at least one volatile breathing compound detector includes an electrochemical sensor having a response rate of up to 90% of a maximum response value in approximately 30 seconds.
In some embodiments, the at least one volatile breathing compound detector is coupled to the gas sampling line via entrance and exit adapters, wherein the adapters are configured to allow a smooth and predominantly laminar flow through the entrance and the exit of a gas sensor of the at least one volatile breathing compound detector. In some embodiments, the adapters include an inlet at a center of and an outlet at a periphery of the respective sensors allowing an approximately 90-degree deflection of the gas flow into and out of the gas sensor of the at least one volatile breathing compound detector.
In some embodiments, the device is configured for spot checking the level of volatile breathing compound in the patient respiratory gas. In some embodiments, at least one component of the device is produced by means of additive manufacturing of a plastic material.
In some embodiments, the at least one component is covered with an anti-stick material. In some embodiments, the anti-stick material includes a resin.
In accordance with one embodiment, the pump is arranged downstream of the at least one volatile breathing detector when the patient respiratory gas flows in the reverse direction. This allows the pump to be situated where it is interfering the least with other components of the device, and where is reaches best possible performance.
In another embodiment, a device configured for monitoring a concentration of at least one volatile breathing compound in respiratory gases of patients can include: a patient respiratory gas interface including a mouthpiece for the patient to blow respiratory gas into; a connector adapted to couple the patient respiratory gas interface to a gas conduit, the gas conduit leading the respiratory gas through a flow meter and a valve, the flow meter configured to measure the patient respiratory gas flux, wherein the gas conduit is configured to further lead the patient respiratory gas through an inlet into an intermediate gas storage, which is open-ended via an exhaust outlet to let patient respiratory gas exhausts in excess of the intermediate gas storage volume out of the same, in response to the flow meter sensing the expiration of the patient respiratory gas flux (i.e. the discontinuation of the exhaled breath, closing the valve); and a pump configured to draw the patient respiratory gas with a predefined second flux level in the reverse direction out of a sampling gas outlet of the intermediate gas storage and into a gas sampling line, in which the exhaled concentrations of the at least one volatile breathing compound are determined by corresponding at least one volatile breathing compound detector.
In some embodiments, the volatile breathing compound includes at least one of fractional exhaled nitric oxide (FeNO), exhaled carbon monoxide (eCO), hydrogen (H2), hydrogen sulfide, (H2S) and ammonia (NH3). In view of the above volatile breathing compounds to be measured, it is suitable that corresponding at least one breathing compound detector provided for measurement is at least one of an NO detector, a CO detector, an H2 detector, a H2S detector, and an NH3 detector. Different compounds are to be used for different diagnostic purposes, and although the description has been discussing measurement of NO and CO, those are replaceable with any of the above-mentioned compounds.
In some embodiments, the flow meter comprises a feedback display unit adapted to display to the patient the actual exhaled patient respiratory gas flux in relation to the predefined first flux level while the patient is exhaling. This feedback unit assists the patient in blowing in the mouthpiece with a pressure that is suitable for the flow to remain laminar and easy to measure with sufficient accuracy for it to be used as basis for a correct diagnose.
In some embodiments, the flow meter is a differential pressure gauge. This is an inexpensive sensor that still yields very good measurement accuracy compared to many other sensors that may yield similar results at significant higher production costs.
In some embodiments, the predefined first flux of respiratory gases is between 30-70 ml/s, between 40-60 ml/s, or at least 50 ml/s. This flux is optimal from the point of view of being measurable with good accuracy and reduce the risk of mixing early portions, such as the initial part of the exhaled breath, with late portions, such as the last part of the exhaled breath of a patient's respiratory gas from a single breath.
In some embodiments, a winding inner volume of the intermediate gas storage has rounded corners. This further reduces the risk for creation of turbulent flow when gas flows around sharp corners with reasonably high pressure.
In some embodiments, the intermediate gas storage has a patient respiratory gas intake volume of approximately 40-80 ml, approximately 55-65 ml, or approximately 60 ml. This prevents the undesired and potentially contaminated early portions of the patient's exhaled breath from being measured, since exhaled gas in excess of the volume of the intermediate gas storage is allowed to exit through the exhaust outlet.
In some embodiments, the patient respiratory gas is drawn in the reverse direction through the gas sampling line with a predefined second flux level between 40-80 ml/min, between 50-70 ml/min, or at least 60 ml/min.
In some embodiments, the NO detector and/or the CO detector are electrochemical sensors having a response rate of up to 90% of the maximum response value in approximately 30 seconds. Again, an electrochemical sensor is an inexpensive sensor that still yields very good measurement accuracy compared to many other sensors that may yield similar results at significant higher production costs.
In some embodiments, the sensors of the NO detector and/or the CO detector are coupled to the gas sampling line via adapters, the adapters being adapted to allow a smooth and laminar flow through the entrances and the exits the gas respective sensors. This further increases the measurement accuracy and reduces excess blowing resistance for the patient.
In some embodiments, the adapters have an inlet at the center of and an outlet at the periphery of the respective sensors allowing an approximately 90-degree deflection of the gas flow into and out of the gas sensor. The advantage of this is the simple and relatively inexpensive construction of the gas sampling line.
In some embodiments, the device is configured for spot-checking the levels of NO and CO in the patient respiratory gas.
In some embodiments, at least one component of the device has been produced by means of additive manufacturing of a structurally strong, stiff, and sturdy plastic material, such as acrylonitrile butadiene styrene (ABS).
In another embodiment, a system for monitoring a concentration of at least one volatile breathing compound in respiratory gases of patients can include: a patient respiratory gas interface including a mouthpiece for the patient to blow a respiratory gas into; an intermediate gas storage is in fluid communication with the patient respiratory gas interface and configured to receive the respiratory gas, wherein the intermediate gas storage is open-ended via an exhaust outlet; a flow meter and a valve in fluid communication with the patient respiratory gas interface and the intermediate gas storage, wherein the flow meter is configured to measure a predefined first flux level of a patient respiratory gas flux and to let patient respiratory gas exhausts in excess of a volume of the intermediate gas storage out of the exhaust outlet in response to the flow meter sensing an expiration of the patient respiratory gas flux, the valve closing at the sensing of the expiration of the patient respiratory gas flux; and at least one volatile breathing compound detector connected to a sampling gas outlet of the intermediate gas storage and configured to determine exhaled concentrations of the at least one volatile breathing compound from a predefined second flux level of the patient respiratory gas.
In some embodiments, the system includes a pump connected to the intermediate gas storage and configured to draw the patient respiratory gas with the predefined second flux level in a reverse direction out of the sampling gas outlet of the intermediate gas storage to the at least one volatile breathing compound detector. In some embodiments, the pump is arranged downstream of the at least one volatile breathing detector when the patient respiratory gas flows in the reverse direction.
In some embodiments, the system includes a connector adapted to couple the patient respiratory gas interface to a gas conduit, wherein the gas conduit is configured to lead the patient respiratory gas through the flow meter and the valve. In some embodiments, the gas conduit further leads the patient respiratory gas through an inlet into the intermediate gas storage.
In some embodiments, the at least one volatile breathing compound includes at least one of fractional exhaled nitric oxide (FeNO), exhaled carbon monoxide (eCO), hydrogen (H2), hydrogen sulfide, (H2S) and ammonia (NH3). In some embodiments, the corresponding at least one breathing compound detector is at least one of an NO detector, a CO detector, an H2-detector, a H2S-detector, and an NH3-detector.
In some embodiments, the system includes a feed-back display unit in electrical communication with the flow meter and configured to display to the patient an actual exhaled patient respiratory gas flux in relation to the predefined first flux level while the patient is exhaling. In some embodiments, the flow meter includes a differential pressure gauge.
In some embodiments, the predefined first flux of respiratory gases is between 30-70 ml/s, between 40-60 ml/s, or at least 50 ml/s. In some embodiments, the winding inner volume of the intermediate gas storage includes rounded corners.
In some embodiments, the patient respiratory gas is drawn in the reverse direction through the gas sampling line with a predefined second flux level of 40-80 ml/min, of 50-70 ml/min, or of 60 ml/min. In some embodiments, the intermediate gas storage has a patient respiratory gas intake volume of approximately 40-80 ml, approximately 55-65 ml, or approximately 60 ml.
In some embodiments, the at least one volatile breathing compound detector includes an electrochemical sensor having a response rate of up to 90% of a maximum response value in approximately 30 seconds. In some embodiments, the at least one volatile breathing compound detector is coupled to the gas sampling line via entrance and exit adapters, wherein the adapters are configured to allow a smooth and predominantly laminar flow through the entrance and the exit of a gas sensor of the at least one volatile breathing compound detector.
In some embodiments, the adapters include an inlet at a center of and an outlet at a periphery of the respective sensors allowing an approximately 90-degree deflection of the gas flow into and out of the gas sensor of the detector. In some embodiments, the system is configured for spot checking the level of volatile breathing compound in the patient respiratory gas.
In some embodiments, the at least one component of the system is produced by means of additive manufacturing of a plastic material. In some embodiments, the at least one component is covered with an anti-stick material. In some embodiments, the anti-stick material includes a resin.
In some embodiments, the intermediate gas storage includes a winding inner volume. In some embodiments, the winding inner volume of the intermediate gas storage includes rounded corners.
All of the embodiments described above are combinable with each other without departing from the intended scope of protection.
Various implementations will be described hereinafter with reference to the accompanying drawings. These implementations are illustrated and described by example only and are not intended to limit the scope of the disclosure. In the drawings, similar elements have similar reference numerals. It is to be understood that the accompanying drawings, which are incorporated in and constitute a part of this specification, are for the purpose of illustrating concepts disclosed herein and may not be to scale.
The present disclosure may be understood by reference to the following detailed description. It is noted that, for purposes of illustrative clarity, certain elements in various drawings may not be drawn to scale, may be represented schematically or conceptually, or otherwise may not correspond exactly to certain physical configurations of embodiments.
Although several embodiments, examples, and illustrations are disclosed below, it will be understood by those of ordinary skill in the art that the inventions described herein extend beyond the specifically disclosed embodiments, examples, and illustrations and includes other uses of the inventions and obvious modifications and equivalents thereof. Embodiments are described with reference to the accompanying figures, wherein like numerals refer to like elements throughout. The terminology used in the description presented herein is not intended to be interpreted in any limited or restrictive manner simply because it is being used in conjunction with a detailed description of some specific embodiments of the inventions. In addition, embodiments can comprise several novel features. No single feature is solely responsible for its desirable attributes or is essential to practicing the inventions herein described.
Beginning with the examination of nitric oxide, so-called fractional exhaled nitric oxide (FeNO) devices have been developed. Generally, they can be categorized as devices that relate to a novel medical technology used to aid in the diagnosis of for example asthma. FeNO devices are designed to measure fractional exhaled nitric oxide in the breath of patients. Nitric oxide (NO) is one among a plurality of volatile breathing compounds that can be used as a biomarker for asthma. Presence of NO in certain concentrations may provide an indication of the level of inflammation in the lungs of a patient. FeNO testing is typically arranged to produce a FeNO score according to a predefined scale, which gives a value to the level of inflammation and thus can be used to aid in the detection and diagnosis of asthma. Although FeNO and devices for its measurement are primarily to be seen as a diagnostic tool, it can have an additional use in the ongoing monitoring of chronic asthma.
Besides NO above, carbon monoxide (CO) is another volatile breathing compound that can exhibit properties that also make this compound suitable for use as a biomarker. CO is a ubiquitous environmental product of breathing combustion, which is also produced endogenously in the body, as a by-product of heme metabolism. CO binds to hemoglobin, resulting in decreased oxygen delivery to bodily tissues at toxicological concentrations. However, at lower concentrations (i.e., normal physiological concentrations) CO may have endogenous roles as a potential signaling mediator in vascular function and cellular homeostasis. Similar to fractional exhaled nitric oxide (FeNO), exhaled CO (eCO) has been evaluated as a promising candidate breath biomarker of pathophysiological states, including smoking status, and inflammatory diseases of the lung and other organs. As for the case of NO, which has been briefly described above, eCO values have been evaluated as potential indicators of inflammation in asthma, stable chronic obstructive pulmonary disease (COPD) and exacerbations, cystic fibrosis, lung cancer, during surgery or during critical care. The utility of eCO as a marker of inflammation, and potential diagnostic value still remains to be fully characterized. Among other volatile breathing compounds that are mentioned in the scientific literature as candidate “medicinal gases” with therapeutic potential, CO has been shown to display promising properties, acting as an effective anti-inflammatory agent in preclinical animal models of inflammatory disease, acute lung injury, sepsis, ischemia/reperfusion injury and organ graft rejection. Current and future clinical trials will further evaluate the value and clinical applicability of this gas as a suitable biomarker and/or therapeutic in human disease.
With respect to NO, it is produced in a patient's body by endothelial cells on the inner surface of blood vessels, nerve cells and inflammatory cells. In the human respiratory system, alveolar cells, the respiratory tract epithelium, or another type of cells in contact with the lungs or the airways of the respiratory tract produce endogenous NO. This NO is secreted into the air in the respiratory ducts and/or lungs of the patient. In result of a patient exhaling, the concentration of the NO content in the exhaled respiratory air can be determined.
The article “An official ATS clinical practice guideline: interpretation of exhaled nitric oxide levels (FENO) for clinical applications”, R A Dweik, P B Boggs et al., Am J Respir Crit Care Med, Vol 184., pp 602-615, 2011, introduces a scientific study in which it is shown that smoking reduces FeNO. Experimentally, the value of exhaled nitric oxide is used to identify asthma in smoking patients with asthma-like symptoms. The study further concludes that FeNO cut-off levels needed to achieve high sensitivity or specificity were lower in current smokers. Therefore, it is meant that measuring the exhaled concentration of FeNO together with eCO concentration allows to determine lung inflammation and symptoms with smokers as well as healthy patients.
Hence, an evaluation of the production of endogenous NO in the lungs and respiratory ducts provides a measurement of the condition and/or function of the lungs and respiratory ducts. The accuracy of the measurement of NO in respiratory air is surprisingly good because NO measured in the respiratory air is unlikely to emanate from other organs in the body since NO produced in other locations of the body would immediately bind to the blood's hemoglobin. This would result in the NO content being broken down subsequently leaving no measurable remains.
NO is formed endogenously along the whole breathing pathway (i.e., in the oral cavity) in the sinuses, in the nose, in the trachea past the larynx, in the bronchia, and within the “free space” in the lungs, as well as in the inner blood-filled parts of the lungs. As the diagnostic purpose is directed to the condition of the lungs and/or respiratory tract, the NO generated in the volume of the mouth, nose, throat, and bronchus are of less interest and should advantageously be disregarded.
In some instances, the volume of the mouth, nose, throat, and bronchus is denoted as a so-called “dead space”. An approximation made in order to quantify this volume and adapt to varying circumstances is 2 ml per kg of body weight, although certain deviations are natural to occur with regard to patients' differing physique, age, sex, and further due to the possible use of breathing aids such as tracheotomy or intubation tubing.
There can be significant advantages from a diagnostic perspective with collecting a sample for NO measurement towards the end of an exhalation of a patient's breath. As the last part of a breath is to be collected, the initial phase of the patient's breath can be discarded by allowing a volume of the patient's breath exceeding the volume of the undesired dead space to flow through the measuring device as exhaust before starting sampling of the breath.
Described herein are systems, devices, and methods for monitoring patient respiratory gas content. A device is proposed for monitoring a concentration of at least one volatile breathing compound in respiratory gases of patients, comprising a patient respiratory gas interface, comprising a mouthpiece for the patient to blow respiratory gas into, a connector adapted to couple the patient respiratory gas interface to a gas conduit, the gas conduit leading the gas through a flow meter and a valve, the flow meter being adapted to measure the patient respiratory gas flux, the gas conduit further leading the patient respiratory gas through an inlet into an intermediate gas storage, which is open-ended via an exhaust outlet to let patient respiratory gas exhausts in excess of the intermediate gas storage volume out of the same. In response to the flow meter sensing the expiration of the patient respiratory gas flux, i.e., the discontinuation of the exhaled breath, closing the valve.
Furthermore, a pump can be configured to draw the patient respiratory gas with a predefined second flux level in the reverse direction out of a sampling gas outlet of the intermediate gas storage and into a gas sampling line, in which the exhaled concentrations of the at least one volatile breathing compound are determined by corresponding at least one volatile breathing compound detector.
The device 100 can include an intermediate gas storage 150 having an inner winding volume, which can be open-ended via an exhaust outlet 156 to let out patient respiratory gas exhausts in excess of a volume of the intermediate gas storage 150. The intermediate gas storage 150 can have a patient respiratory gas intake volume of approximately 10-120 ml, approximately 20-100 ml, approximately 30-90 ml, approximately 40-80 ml, approximately 55-65 ml, or approximately 60 ml. In some embodiments, the winding inner volume of the intermediate gas storage 150 can include rounded corners. In response to the flow meter 132 sensing the expiration of the patient respiratory gas flux (i.e., the discontinuation of the exhaled breath), the valve 134 can be closed. In some embodiments, the gas conduit 140 can further lead the patient respiratory gas through an inlet 152 into the volume of the intermediate gas storage 150.
At least one volatile breathing compound detector 190′, 190″ can be connected to a sampling gas outlet 154 of the intermediate gas storage 150 and configured to determine exhaled concentrations of the at least one volatile breathing compound from a predefined second flux level of the patient respiratory gas. In some embodiments, a pump 170 can be capable of and arranged to draw the patient respiratory gas with the predefined second flux level in the reverse direction out of the sampling gas outlet 154 of the intermediate gas storage 150 and into a gas sampling line 180. The predefined second flux level can be 10-120 ml/min, 20-100 ml/min, 40-80 ml/min, of 50-70 ml/min, and/or of 60 ml/min. This can be where the exhaled concentrations of the at least one volatile breathing compound are determined by the corresponding at least one volatile breathing compound detector 190′, 190″. In some embodiments, the detectors 190′, 190″ can include entrance and exit adapters 192′, 194′; 192″, 194″ respectively, for coupling to the gas sampling line 180. The adapters 192′, 194′; 192″, 194″ of the detectors 190′, 190″ respectively, can be constructed so as to allow a smooth and predominantly laminar flow through the entrance 192′, 192″ and the exit 194′, 194″ of the gas sensor of the detectors 190′, 190″. The adapters 192′, 194′; 192″, 194″ can include an inlet at a center of and an outlet at a periphery of the respective sensors allowing an approximately 90-degree deflection of the gas flow into and out of the gas sensor of the at least one volatile breathing compound detector 190′, 190″. The volatile breathing compound can include at least one of fractional exhaled nitric oxide (FeNO), exhaled carbon monoxide (eCO), hydrogen (H2), hydrogen sulfide, (H2S) and/or ammonia (NH3). In some embodiments, the at least one volatile breathing compound detector 190′, 190″ can include an electrochemical sensor having a response rate of up to 90% of a maximum response value in approximately 30 seconds.
The intermediate gas storage 150 can be a variety of conceivable storages, such as a maze, a labyrinth, a buffer, or a hose that has been coiled up to reduce the space taken up by the volume. It is not the shape of the storage volume as such that matters, but rather that the outer dimensions of the volume are designed to avoid bulky constructions to achieve slenderer and easier to produce shapes of the device. The size and shape of the tubular shape of the inner volume, however, can be shaped to allow for a gas flow that remains laminar under pressure to yield predictable measurement results. It can also be tubular so as to reduce the risk of mixing the initial portions of a patient's breath with the terminal portion of the same, which terminal portion is the more interesting to analyze from a diagnostic perspective. Furthermore, it can be advantageous to allow the exhalation flow from the patient to settle to a continuous flow, such that a steady level of exhaled NO is reached. The state which is sought after is known as a plateau of the exhalation.
The device 100 can be constructed so as to exert a suitable blowing resistance for the patient. With this in mind, it reflects the skilled person's choice components and of their dimensions, such as diameter of conduits, mouthpiece, gas connector inlets, and outlets of gas. For optimum function of the device 100 and associated system, is important that there is a suitable resistance for the patient to experience an overpressure in the mouth while exhaling, because that displaces nasal air which would otherwise potentially contaminate the measurement with undesired impurities, thereby reducing the likelihood of determining results that could diagnose the risk for or presence of inflammatory diseases in the lungs.
The buffered exhaled breath can be pumped out of the sampling gas outlet 154 from the intermediate gas storage 150 by means of the pump 170, which can be placed downstream of the detectors 190′, 190″ when the patient respiratory gas flows in the reverse direction. The pump 170 could, for example, be a membrane pump, which can make sure that there can be no backflow through the pump 170 contaminating the sample breath in the buffer chamber during the inhalation and/or exhalation phase. The pump 170 can be expunging the gases at the rate of approximately 50-250 ml/min, 100-200 ml/min, 120-180 ml/min, of 140-160 ml/min, and/or of approximately 150 ml/min. The NO and/or CO detectors can be electrochemical sensors with a relatively slow response, which can lead to the inclusion of the intermediate gas storage 150 and the pump 170. The pump 170 can flow the collected sample breath over the sensor at such a rate that the detectors 190′, 190″ have sufficient time to respond to the NO and/or CO content of the breath and thus being able to accurately sense inflammation in the airways indicated by the NO and/or CO content.
The relation between the volume of the intermediate gas storage 150, the second predetermined flux, and the response time of detectors 190′, 190″ can depend on each other. Which gas storage volumes, flow rates, and detector performance for optimum function in relation to cost is something that a skilled person will readily be able to determine and optimize based on his/her general technical ability and the easily recognizable correspondence between the relevant rates and relations already known in the technical field.
In manufacturing the device 100, at least one component of the device 100 can produced by means of additive manufacturing of a plastic material. For example, any component of the device 100 of a structurally strong, stiff, and sturdy plastic material, such as acrylonitrile butadiene styrene (ABS). Additionally, at least one component can be covered with an anti-stick material such as a resin (e.g., Teflon®).
This device can be advantageous in many ways. One of the advantages is that the undesired portion of a patient's respiratory gas contained in a breath, in the prior art also called the dead space, can be completely avoided without approximating individual deviations in lung volume or blowing capacity. Moreover, the device does not need to be adjusted individually in dependence of a patient's physique, age, sex, or to possible external factors like use of breathing aids such as tracheotomy or intubation tubing. One device can be able to serve patients equally well, without the replacement components or adjusting any settings of the device.
The inventors realized that the last portion of the breath is afflicted with fewer sources of measurement errors, and that the so-called desired plateau for optimal measurement precision is present towards the very end of each breath. Therefore, according to one embodiment, an NO detector, an CO detector and/or possibly other types of detectors will be sampling the patient respiratory gas on the last part of the exhaled gas volume, irrespective of individual deviations, hence further potentially decreasing the influence of various sources of error and therefore enhancing the accuracy and repeatability of measurements.
Yet another advantage is that by measuring the very last part of the breath, a shorter time of breath may be sufficient for obtaining an acceptable measurement result. This is of particular importance as certain patients with a more severe condition and/or experiencing physiological constraints, may find it difficult to make an exhalation for a longer period in time, i.e., for approximately ten seconds or more. However, given the construction and/or function of the device, about 5 seconds of exhalation may be sufficient. This exhalation is divided in two, of which the first half is disposed of and the rest fills the intermediate gas storage. However, for patients who are able to exhale for longer periods, the inventive device of course works just as well. The recommendation is still to obtain measurements on an exhalation over 10 seconds or longer.
Medical devices for monitoring content and/or concentrations of certain possible biomarkers in respiratory gases can be simple and robust from a constructional point of view. In some embodiments, a device is proposed in which a single valve can be sufficient in order to achieve the intended function. Prior art solutions are more complex from a constructional view, since they require at least two valves, which valves for functional reasons need to operate in synchronization with each other for comparable performance. By the device, a simpler device is achieved in which the requirement for synchronization is completely avoided, which, as a consequence, provides for a more robust device, which is less prone to dysfunction. Due to reduced complexity, it is also potentially less costly to produce than the estimated production costs of comparable devices according to the prior art.
Reversal of the flow direction can make it possible to close an already existing valve which is provided towards the patient's end of the conduit. Placing the single valve at the end of the patient even further reduces the risk for sampling gas to be contaminated by exhaled gas from the patient during the measurement phase.
Spirometry is a well-known physiological test that measures how an individual inhales or exhales volumes of air as a function of time. The primary signal measured in spirometry may be volume or flow. Physiologists describe spirometry as invaluable as a screening test of respiratory health generally in the same way that blood pressure has long provided important information about general cardiovascular health.
However, on its own, spirometry does not lead clinicians directly to an etiological diagnosis, particularly inflammatory diseases in the lungs. See further the review article Standardization of spirometry, Eur Respir J 2005, 319-338, Series “ATS/ERS Task Force: Standardisation of Lung Function Testing”, V. Brusasco, R. Crapo and G. Viegi (ed.). In view of this, it is proposed that spirometry can be combined with measurements of a variety of volatile breathing compounds used for breath gas analyses, in particular using relatively slow sensors, such as electrochemical sensors.
For the sake of clarity and conciseness, it is to be mentioned that patients according to this disclosure may or may not exhibit lung inflammation or similar symptoms, such as asthma or early stages of the same. However, albeit not yet exhibiting or ever exhibiting any symptoms, as a definition of the term patients is here meant anyone who is under examination for the potential presence of inflammatory diseases in the lungs. In addition to NO and CO, which have been described above, some embodiments may also relate to monitoring of other volatile breathing compounds like H2 (hydrogen), H2S (hydrogen sulfide) or NH3 (ammonia).
As soon as a flow meter 132 at block S30 has detected that a patient has reached the end of their actual exhalation, the valve 134 can be closed at block S40 so as to avoid any gas entering the gas conduit 140 from which the gas was lead through mouthpiece, gas interface flow meter 132, and valve 134 into the intermediate gas storage 150 via an inlet 152.
As soon as a pump 170 starts to exert its pumping energy on the gas content in the intermediate gas storage 150, pump 170 at block S50 can draw exhaled gas out of intermediate storage 150 in the reverse direction and through an outlet 154 to a gas sampling line 180. Then at block S60, the gas passes detectors 190′, 190″ by which at least one volatile breathing compound is determined.
The device 100 can be used in a standalone manner and/or in combination with other devices and/or sensors. In some embodiments, as shown in
Optionally, the device 100 can be integrated with more sensors and/or configured to connect to a plurality of external sensors, wirelessly or with a connecting cable. The connecting cable can be a universal connector configured to connect to any of the medical devices and/or sensors disclosed herein to provide communication between the device 100 and the connected medical devices and/or sensors. The cable can optionally include a board-in-cable device that includes its own processor, but may not include its own display.
Unless the context clearly requires otherwise, throughout the description and the claims, the words “comprise,” “comprising,” “include,” “including” and the like are to be construed in an inclusive sense, as opposed to an exclusive or exhaustive sense; that is to say, in the sense of “including, but not limited to.” The word “coupled”, as generally used herein, refers to two or more elements that may be either directly connected, or connected by way of one or more intermediate elements. Likewise, the word “connected”, as generally used herein, refers to two or more elements that may be either directly connected, or connected by way of one or more intermediate elements. Additionally, the words “herein,” “above,” “below,” and words of similar import, when used in this application, shall refer to this application as a whole and not to any particular portions of this application. Moreover, as used herein, when a first element is described as being “on” or “over” a second element, the first clement may be directly on or over the second element, such that the first and second elements directly contact, or the first element may be indirectly on or over the second element such that one or more elements intervene between the first and second elements. Where the context permits, words in the above Detailed Description using the singular or plural number may also include the plural or singular number respectively. The word “or” in reference to a list of two or more items, that word covers all of the following interpretations of the word: any of the items in the list, all of the items in the list, and any combination of the items in the list.
Moreover, conditional language used herein, such as, among others, “can,” “could,” “might,” “may,” “e.g.,” “for example,” “such as” and the like, unless specifically stated otherwise, or otherwise understood within the context as used, is generally intended to convey that certain embodiments include, while other embodiments do not include, certain features, elements and/or states. Thus, such conditional language is not generally intended to imply that features, elements and/or states are in any way required for one or more embodiments.
Several illustrative examples of systems and methods for monitoring respiratory gases have been disclosed. Although this disclosure has been described in terms of certain illustrative examples and uses, other examples and other uses, including examples and uses which do not provide all of the features and advantages set forth herein, are also within the scope of this disclosure. Components, elements, features, acts, or steps may be arranged or performed differently than described and components, elements, features, acts, or steps may be combined, merged, added, or left out in various examples. All possible combinations and subcombinations of elements and components described herein are intended to be included in this disclosure. No single feature or group of features is necessary or indispensable.
Certain features that are described in this disclosure in the context of separate implementations may also be implemented in combination in a single implementation. Conversely, various features that are described in the context of a single implementation also may be implemented in multiple implementations separately or in any suitable subcombination. Moreover, although features may be described above as acting in certain combinations, one or more features from a claimed combination may in some cases be excised from the combination, and the combination may be claimed as a subcombination or variation of a subcombination.
Further, while illustrative examples have been described, any examples having equivalent elements, modifications, omissions, and/or combinations are also within the scope of this disclosure. Moreover, although certain aspects, advantages, and novel features are described herein, not necessarily all such advantages may be achieved in accordance with any particular example. For example, some examples within the scope of this disclosure achieve one advantage, or a group of advantages, as taught herein without necessarily achieving other advantages taught or suggested herein. Further, some examples may achieve different advantages than those taught or suggested herein.
Some examples have been described in connection with the accompanying drawings. The figures may or may not be drawn and/or shown to scale, but such scale should not be limiting, since dimensions and proportions other than what are shown are contemplated and are within the scope of the disclosed invention. Distances, angles, etc. are merely illustrative and do not necessarily bear an exact relationship to actual dimensions and layout of the devices illustrated. Components may be added, removed, and/or rearranged. Further, the disclosure herein of any particular feature, aspect, method, property, characteristic, quality, attribute, element, or the like in connection with various examples may be used in all other examples set forth herein. Additionally, any methods described herein may be practiced using any device suitable for performing the recited steps.
For purposes of summarizing the disclosure, certain aspects, advantages, and features of the inventions have been described herein. Not all, or any such advantages are necessarily achieved in accordance with any particular example of the inventions disclosed herein. No aspects of this disclosure are essential or indispensable. In many examples, the devices, systems, and methods may be configured differently than illustrated in the figures, or description herein. For example, various functionalities provided by the illustrated modules may be combined, rearranged, added, or deleted. In some implementations, additional or different processors or modules may perform some or all of the functionalities described with reference to the examples described and illustrated in the figures. Many implementation variations are possible. Any of the features, structures, steps, or processes disclosed in this specification may be included in any example.
Any and all applications for which a foreign or domestic priority claim is identified in the Application Data Sheet as filed with the present application are hereby incorporated by reference under 37 CFR 1.57. This application claims the priority benefit of U.S. Provisional Patent Application No. 63/489,145 filed on Mar. 8, 2023, entitled “SYSTEMS AND METHODS FOR MONITORING RESPIRATORY GASES,” which is incorporated by reference herein in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| 63489145 | Mar 2023 | US |
