Method for quantitative collection and measurement of partial components of human exhaled breath, medium and device

Abstract

The present application relates to the field of data processing, in particular to a human exhaled air quantitative collection and partial component measurement method, medium and equipment. It comprises: according to the corresponding down-flow signal transmission time and up-flow signal transmission time of each collection time; generating the fluid velocity of each collection time; and generating the collection amount of human exhaled air components. Through the electrochemical sensor, the volume content of part of the gas components in the exhaled air is measured. In the present application, the exhaled air gas flow rate is obtained by setting the ultrasonic flow meter group on the gas collection pipeline, and then the change relationship of the flow rate with time can be obtained. The total flow of the exhaled gas in a certain time period is calculated by definite integral, and then the volume of the human exhaled air in the time period can be quantitatively collected. In addition, through the electrochemical or infrared light measurement method, after the volume of the human exhaled air is measured, the function of measuring part of the components (such as NO) in the exhaled air is also possessed.

Description

TECHNICAL FIELD

[0001] The present application relates to the field of data processing, in particular to a human exhaled breath quantitative collection and partial component measurement method, medium and equipment. BACKGROUND

[0002] Human exhaled breath can reflect the health status of people, and exhaled breath component detection has been increasingly concerned in the diagnosis and treatment of respiratory system related diseases in recent years. The detection results can be used to evaluate the degree of airway inflammation and oxidative stress of patients, and it is a non-invasive detection method for patients. It can also be used for detection of respiratory pathogens, and has the advantages of simplicity, easy operation, good repeatability, etc. It is suitable for patients with respiratory system related diseases and children, including infants. Respiratory diseases include asthma, chronic obstructive pulmonary disease, etc. It provides a new means for monitoring the progress and treatment effect of lung related diseases.

[0003] Quantitative collection of human exhaled breath is the primary problem to be solved for exhaled breath component detection, and the collection method will directly affect the accuracy of the detection results and the reliability of the response to the pathological and physiological changes of the lungs and airways.

[0004] For the collection of human exhaled breath components, the existing devices condense the exhaled breath to form a condensate (exhaled breath condensate, EBC for short), and collect it, which is called an exhaled breath condensate collector or collector, such as ECoScreen I, ECoScreen II, RTube, Anacon, TurboDeccs, etc. Each collector has its own characteristics and range of use. Some EBC collectors have an exhalation tube directly inserted into the oral cavity to blow air, which will mix with saliva and blow out with the exhaled breath. And EBC collection often uses different condensation methods, mainly including water bath, compressor and semiconductor refrigeration methods. The effects of various refrigeration methods are different, resulting in different amounts and components of EBC collected, which in turn leads to the difficulty of horizontal comparison of EBC measurement results in different research groups. More importantly, exhaled breath condensate only collects gas components that can be condensed into liquid at a certain temperature, and gaseous components that have not been condensed or have not been fully condensed, such as nitric oxide, carbon monoxide and carbon dioxide, cannot be collected and measured, which makes it difficult to obtain the proportion or content of each component in the exhaled breath. Therefore, the exhaled breath condensate collector or collector in the existing device cannot quantitatively obtain the specific volume data of the exhaled breath group. SUMMARY

[0005] In view of the above technical problems, the technical scheme adopted by the present application is:

[0006] According to one aspect of the present application, there is provided a method for quantitative collection and partial component measurement of human exhaled breath, applied to a gas measurement assembly, the gas measurement assembly comprising a gas collection pipeline and an ultrasonic flowmeter group arranged on the wall of the gas collection pipeline, the ultrasonic flowmeter group comprising two ultrasonic sensors;

[0007] The method comprises the following steps:

[0008] In a preset collection period, the downstream signal transmission time T and the upstream signal transmission time t obtained by the ultrasonic flowmeter group at each collection time are obtained;

[0009] According to the T and t corresponding to each collection time, the fluid velocity V corresponding to each collection time is generated; V satisfies the following condition:

[0010] ;

[0011] Wherein, L is the distance between the two ultrasonic sensors in the ultrasonic flowmeter group, L=D / sinφ; φ is the included angle between the line connecting the two ultrasonic sensors and the axial direction of the pipeline; D is the inner diameter of the gas collection pipeline;

[0012] According to the fluid velocity corresponding to each collection time, the collection amount W of the components of the human exhaled breath in the preset collection period is generated; W satisfies the following condition:

[0013] ;

[0014] Wherein, a and b are the start time and end time of the preset period respectively; S is the cross-sectional area of the gas collection pipeline;

[0015] The gas measurement assembly further comprises a cold trap;

[0016] The gas collection pipeline is connected to the inlet of the cold trap, and the outlet of the cold trap is connected to the working electrode of the sensor or the infrared light path through a pipeline;

[0017] The volume content of the partial gas components in the exhaled breath is measured by the sensor.

[0018] According to a second aspect of the present application, there is provided a non-transitory computer readable storage medium, which stores a computer program, and the computer program is executed by a processor to implement the above-mentioned method for quantitative collection and partial component measurement of human exhaled breath.

[0019] According to a third aspect of the present application, there is provided an electronic device, comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, and the processor executes the computer program to implement the above-mentioned method for quantitative collection and partial component measurement of human exhaled breath.

[0020] The present application has at least the following beneficial effects:

[0021] In the present application, since the flow rate of the airflow generated by the human body during breathing is not constant, the flow rate of the exhaled gas at the monitoring point at different times is obtained by arranging the ultrasonic flowmeter group on the gas collection pipeline, and then the relationship between the flow rate and time is obtained. Then, the total flow of the exhaled gas in a certain time period is calculated by definite integral, and then the volume of the exhaled gas of the human body in the time period is quantitatively collected.

[0022] At the same time, when the total amount of the exhaled gas of the human body is calculated by the ultrasonic flowmeter group, it can be ensured that there is no obstacle in the entire airway, ensuring the patency of the entire airway, and will not cause respiratory obstruction to the user (especially patients with impaired lung function), and will not absorb or capture the gas components in the exhaled gas, thereby ensuring the accuracy of the final measurement result, and being more convenient for patients to use.

[0023] In addition, by the method of electrochemical or infrared light measurement, the function of measuring part of the components (such as nitric oxide) in the exhaled gas can be realized after measuring the volume of the exhaled gas of the human body, thereby avoiding the waste of medical resources such as the fatigue of the patient and the reduction of the work burden of the nursing staff. BRIEF DESCRIPTION OF DRAWINGS

[0024] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings needed in the embodiment description will be briefly introduced. Obviously, the drawings in the following description are only some embodiments of the present application, and other drawings can be obtained by those skilled in the art without creative labor.

[0025] Figure 1 The flowchart of the method for quantitatively collecting and measuring part of the components of the exhaled gas of the human body provided by the embodiments of the present application;

[0026] Figure 2 The connection schematic diagram of the gas collection pipeline and the ultrasonic flowmeter group provided by the embodiments of the present application;

[0027] Figure 3 The distribution position schematic diagram of the two ultrasonic flowmeter groups in the cross-sectional direction of the gas collection pipeline provided by the embodiments of the present application;

[0028] Figure 4 The distribution position schematic diagram of the two ultrasonic flowmeter groups on the wall of the gas collection pipeline provided by the embodiments of the present application;

[0029] Figure 5A schematic diagram of the distribution positions of two groups of ultrasonic flowmeters and a calibration flowmeter group on the wall of a gas collection pipeline provided by an embodiment of the present invention;

[0030] Figure 6 A schematic structural diagram of a cold trap provided in an embodiment of the present invention. DETAILED DESCRIPTION

[0031] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without making any creative efforts shall fall within the scope of protection of the present invention.

[0032] As a possible embodiment of the present invention, Figure 1 and Figure 2 As shown, a method for quantitatively collecting exhaled human breath and measuring some of its components is provided. This method is applied to a gas measurement assembly, which includes a gas collection pipeline and an ultrasonic flowmeter assembly mounted on the wall of the pipeline. The ultrasonic flowmeter assembly includes two ultrasonic sensors (A and B in the figure). To ensure uniform laminar flow at the detection location within the pipeline, the straightness of the pipeline must be maintained for a considerable distance before and after the ultrasonic flowmeter assembly to avoid airflow disturbances caused by pipe curvature. Furthermore, to prevent interference from other acoustic components in the hospital environment, the ultrasonic flowmeter assembly can be wrapped with sound-absorbing cotton to provide both sound insulation and heat preservation, thereby improving detection accuracy.

[0033] The method comprises the following steps:

[0034] S100: In a preset collection period, the downstream signal transmission time T and the upstream signal transmission time t obtained by the ultrasonic flow meter group at each collection moment are obtained.

[0035] The ultrasonic sensors are inserted into the corresponding gas collection pipes by a fastening mechanism. Ultrasonic pulses are transmitted and received alternately by the two ultrasonic sensors.

[0036] Specifically, the ultrasound pulses shuttle in the pipe like boats in a river. When there is no flow, the same propagation speed is obtained in all directions. When the ultrasound propagates along the direction of the gas flow, it gets a boost from the gas flow speed in the breath, making the actual propagation speed equal to the speed of sound plus the component of the gas flow speed. Thus the signal propagates slightly faster along the flow direction, corresponding to a downstream signal transmission time T. Conversely, when the ultrasound propagates against the direction of the gas flow, it encounters resistance, making the actual propagation speed equal to the speed of sound minus the component of the gas flow speed. The signal propagates slightly slower against the flow, corresponding to an upstream signal transmission time t. Normally T is less than t.

[0037] S200: generating a fluid speed V corresponding to each acquisition time according to T and t corresponding to each acquisition time. V satisfies the following condition:

[0038] .

[0039] where L is the distance between two ultrasonic sensors in the ultrasonic flow meter group, L = D / sinφ. φ is the included angle between the line connecting the two ultrasonic sensors and the axial direction of the pipe. D is the inner diameter of the gas acquisition pipe.

[0040] Specifically, in this embodiment, because the gas flow direction in the pipe during inhalation is opposite to that during exhalation, T is greater than t. Thus by comparing the size relationship between T and t, the current state of the patient, whether exhalation or inhalation, can be accurately obtained. Further, the flow generated during inhalation can be removed.

[0041] By comparing the propagation time difference of the sound wave when flowing and against the flow, the flow speed of the gas can be calculated. Because the angle φ between the sound wave propagation direction and the gas flow direction affects the propagation time of the sound wave, when calculating, the time difference needs to be divided by cosφ to correct the angle influence.

[0042] Specifically, 1 / T - 1 / t in the formula is actually the reciprocal of the time difference, representing the degree of influence of the gas flow speed on the propagation time of the sound wave. In this use scenario, the breath of a person (especially a patient) is relatively weak, that is, the measured gas flow speed is extremely low. Therefore, for this low flow speed measurement scenario, the calculation formula in this embodiment uses (1 / T - 1 / t) instead of (t - T) to calculate.

[0043] Mathematically, both methods can eventually express the relationship between flow rate and time difference, but the form of (1 / T - 1 / t) mathematically amplifies the impact of flow rate, especially in the case of small flow rate, which improves the sensitivity and accuracy of measurement. This is because when the flow rate is very low, the direct time difference (t-T) will be very small, and any minor measurement error will be significantly amplified, affecting the accuracy of the flow rate. In contrast, using the form of (1 / T - 1 / t), even if the flow rate is very small, the impact of the flow rate can be reflected through the difference in the reciprocal of time, which can better capture the changes in flow rate mathematically, thus providing more stable measurement results under low flow rate conditions.

[0044] In addition, due to the angle φ between the sound wave propagation path and the gas flow direction, it is necessary to multiply cosφ to correct the impact of this angle, ensuring that the calculated flow rate is the correct value along the direction of gas flow.

[0045] Finally, since the distance of sound wave propagation in gas is L, the entire expression L (1 / T - 1 / t) / (2cosφ ) calculates the average flow rate of gas along its flow direction. Multiplying by two is because the sound wave goes back and forth twice, but in this specific application scenario, we only care about the one-way flow rate, so the final result is divided by two.

[0046] S300: According to the fluid velocity corresponding to each collection time, the collection amount W of the components of the human exhaled gas in the preset collection period is generated, and W satisfies the following conditions:

[0047] .

[0048] Where a and b are the start time and end time of the preset period respectively. S is the cross-sectional area of the gas collection pipeline.

[0049] In order to collect enough components of exhaled gas for subsequent research, the subject often needs to face the equipment for 5-10 minutes to exhale and inhale, so the preset collection period is usually 5-10 minutes.

[0050] In this embodiment, by performing definite integral calculation on the function V of flow rate with respect to time within the corresponding time period, and then multiplying the cross-sectional area of the corresponding flow channel, the total gas exhalation amount in the corresponding period can be calculated more accurately.

[0051] Further, as shown in Figure 4 The ultrasonic flowmeter group is arranged in the same area of the gas collection pipeline, and there is an included angle between the two ultrasonic flowmeter groups.

[0052] By arranging multiple ultrasonic flowmeter groups at different angles in the same region, the fluid flow rates in different parts of the same cross section can be measured respectively. Since the airflow of the exhaled gas is usually not in a particularly uniform laminar state in the pipeline, the gas flow rates at different positions in the same cross section can be different. Therefore, by setting multiple measurement points, the average speed value calculated by the final calculation can be more close to the true value.

[0053] The method further includes the following steps:

[0054] S500: Control the two ultrasonic flowmeter groups to send and receive signals at the same acquisition frequency, wherein each time the ultrasonic wave signal is sent, the ultrasonic sensors at different positions in the two ultrasonic flowmeter groups are used as the transmitting end respectively.

[0055] In addition, after multiple measurement points (i.e. ultrasonic flowmeter groups) are set, if multiple ultrasonic waves are sent at the same time, interference between them will occur, but to detect the flow rate at the same position at the same time, two measurement points need to measure at the same time. Therefore, in order to further reduce the interference between the ultrasonic waves in this embodiment, the ultrasonic sensors at different positions in the two ultrasonic flowmeter groups are used as the transmitting end respectively each time the ultrasonic wave signal is sent. Therefore, the sound wave signals of one group propagate along the airflow, and the sound wave signals of the other group propagate against the airflow, so that the propagation speeds of the two sound waves are different, thereby causing misalignment and avoiding mutual interference between the sound waves as much as possible. In addition, as shown in the figure, when the two ultrasonic flowmeter groups are arranged, the connecting line of the two ultrasonic sensors of one group can pass through the axis of the pipeline, and the connecting line of the two ultrasonic sensors of the other group does not pass through the axis of the pipeline, thereby making the ultrasonic propagation routes of the two ultrasonic flowmeter groups not coincide, which can also reduce mutual interference and improve the final calculation accuracy. Figure 3

[0056] S600: According to T and t obtained by the two ultrasonic flowmeter groups respectively at each acquisition time, generate the fluid velocities V1 and V2 corresponding to the two ultrasonic flowmeter groups respectively at each acquisition time.

[0057] In this step, the method for obtaining V1 and V2 is the same as that in S100 and S200.

[0058] S700: According to V1 and V2, generate the acquisition amount W of the components of the exhaled gas of the human body in a preset acquisition period, and W satisfies the following condition:

[0059] .

[0060] Before S700, the method further includes:

[0061] S701: If |V1-V2|>Y1, generate a preset alarm information.​

[0062] In addition, by comparing the difference between the gas flow rates obtained by the two ultrasonic flowmeter groups in real time, it can be determined in time whether at least one of the ultrasonic flowmeter groups is malfunctioning, and an alarm can be sent in time.

[0063] In addition, as shown in Figure 5 The gas measurement assembly further includes a verification flowmeter group, which has the same structure as the ultrasonic flowmeter group and is arranged in a downstream region of the ultrasonic flowmeter group.

[0064] Before S700, the method further includes:

[0065] S702: If |V1-V2|>Y1 at the current acquisition time, V1 and V2 are both retained.

[0066] S703: Obtain V3 and V4 collected at the verification flowmeter group at T 1 z and T 2 z, respectively, where T 1 z is a time corresponding to the current acquisition time plus L1 / V1. T 2 z is a time corresponding to the current acquisition time plus L1 / V2. L1 is the distance between the verification flowmeter group and the ultrasonic flowmeter group in the axial direction of the gas acquisition pipeline.

[0067] S704: If |V3-V1|<Y2, V1 is determined as the fluid velocity corresponding to the current acquisition time, Y1 and Y2 are first and second thresholds, respectively. Y1 and Y2 can be set according to actual scenarios.

[0068] S705: If |V4-V2|<Y2, V1 is determined as the fluid velocity corresponding to the current acquisition time.

[0069] In the embodiment, a verification flowmeter group is additionally provided. After the gas flows through the two ultrasonic flowmeter groups, the gas flows through the region corresponding to the verification flowmeter group downstream of the flow channel, and generally, the flow rate in this region is not greatly attenuated. In addition, the distance between the verification flowmeter group and the ultrasonic flowmeter group is certain, so the time at which the gas flow corresponding to the flow rate reaches the verification flowmeter group can be determined by V1 and V2, respectively, and then V3 and V4 can be measured at the corresponding time. By comparing V3 and V4, respectively, it can be determined again which of the two ultrasonic flowmeter groups is malfunctioning, and the data corresponding to the normal ultrasonic flowmeter group can be retained, so that the experiment can be completed normally and smoothly without the need for the patient to repeat the detection.

[0070] As another embodiment of the present application, as shown in Figure 6As shown, the gas measurement assembly further comprises a cold trap.

[0071] The gas collection conduit is connected to the inlet of the cold trap, and the outlet of the cold trap is connected to the working electrode of the electrochemical sensor or the infrared light path by a conduit (the sensor can also be replaced by other measurement sensors according to the specific measured gas component). The temperature of the cooling surface inside the cold trap is -5℃ to -35℃. The length of the conduit into which the inlet of the cold trap extends is greater than the length of the conduit into which the outlet of the cold trap extends.

[0072] For patients with impaired lung function or airway remodeling, there is a large difference in the volume of exhaled gas at the same time compared with healthy control people, so the component content of the condensate and the gas content of the exhaled gas of the two groups of people have important significance for the progress and treatment of lung and airway diseases. In addition, exhaled nitric oxide (NO) has important significance in respiratory function tests, and its concentration is highly correlated with the number of inflammatory cells, which can be used as a biomarker of airway inflammation. Combined with other components of exhaled gas, it plays an important role in the diagnosis and treatment of respiratory diseases such as airway inflammation. At present, the clinical examination of NO and EBC collection uses separate instrument equipment, and the patient needs to perform repeated inhalation and exhalation operations after checking on one device to another device, while more nurses and more space are required. It leads to patient fatigue during examination, increases the workload of nursing staff, and wastes medical resources.

[0073] S400: Measure the volume content of part of the gas components in the exhaled gas by the sensor. The part of the gas components in the exhaled gas includes nitric oxide, carbon monoxide or carbon dioxide. In this step, an electrochemical sensor can be selected to measure nitric oxide.

[0074] In this embodiment, the content of NO is measured by electrochemical detection method. The concentration of nitric oxide (NO) measured by electrochemical method is based on the oxidation or reduction reaction of nitric oxide on the electrochemical sensor. The electrochemical sensor usually includes a working electrode (WE), a reference electrode (RE) and an auxiliary electrode (AE). When the nitric oxide molecule contacts the surface of the working electrode, an electrochemical reaction occurs, generating a current change, which is proportional to the concentration of nitric oxide. By measuring the current change, the content of nitric oxide can be determined.

[0075] The basic principle of electrochemical method for measuring NO is to use the redox characteristics of NO. Under appropriate potential, nitric oxide can be oxidized on the electrode surface, and oxygen (O2) can be reduced. The specific reaction and calculation are as follows:

[0076] NO + 2H2O → NO3 - + 4H + + 3e -

[0077] O2+2H2O+4e − →4OH −

[0078] M=A x AI

[0079] C=M / Q

[0080] Wherein M is the mass of nitric oxide gas, A is the coefficient, AI is the current intensity change, C is the concentration of exhaled nitric oxide gas, and Q is the volume of exhaled gas.

[0081] The gas collection instrument and the corresponding measurement method in the embodiment can measure the volume of the human exhaled gas and measure part of the components (such as nitric oxide) in the exhaled gas at the same time through the electrochemical measurement method, thereby avoiding the waste of medical resources such as the fatigue of the patient in the examination and the reduction of the work burden of the nursing staff.

[0082] In addition, although the various steps of the method in the present disclosure are described in a specific order in the accompanying drawings, this does not require or imply that the steps must be performed in this specific order, or that all of the steps shown must be performed to achieve the desired results. In addition or alternatively, some steps can be omitted, a plurality of steps can be combined into one step, and / or one step can be divided into a plurality of steps, etc.

[0083] From the above description of the embodiments, those skilled in the art can easily understand that the example embodiments described herein can be implemented by software, or by software in combination with necessary hardware. Therefore, the technical solutions according to the embodiments of the present disclosure can be embodied in the form of a software product, which can be stored in a non-volatile storage medium (which can be a CD-ROM, a U disk, a mobile hard disk, etc.) or a network, and includes a plurality of instructions to make a computing device (which can be a personal computer, a server, a mobile terminal, or a network device, etc.) execute the method according to the embodiments of the present disclosure.

[0084] In the example embodiments of the present disclosure, an electronic device capable of implementing the above method is also provided.

[0085] Those skilled in the art can understand that each aspect of the present disclosure can be implemented as a system, a method or a program product. Therefore, each aspect of the present disclosure can be embodied in the form of a complete hardware embodiment, a complete software embodiment (including firmware, microcode, etc.), or an embodiment combining hardware and software aspects, which can be collectively referred to as "circuitry", "module" or "system" herein.

[0086] The electronic device according to this embodiment of the present application. The electronic device is merely an example and should not bring any limitation to the function and use range of the embodiments of the present application.

[0087] The electronic device is in the form of a general computing device. The components of the electronic device can include, but are not limited to, the at least one processor described above, the at least one memory described above, and a bus that connects different system components, including the memory and the processor.

[0088] The memory stores program codes that can be executed by the processor, so that the processor performs the steps described in the above "Exemplary Method" section according to various exemplary embodiments of the present application.

[0089] The memory can include a readable medium in the form of a volatile memory, such as a random access memory (RAM) and / or a cache memory, and can further include a read-only memory (ROM).

[0090] The memory can also include programs / utilities with a set of (at least one) program modules, such as an operating system, one or more application programs, other program modules, and program data, each of which or some combination of which can include the implementation of a network environment.

[0091] The bus can be one or more of several types of bus structures, including a memory bus or memory controller, a peripheral bus, a graphics acceleration port, a processor or a local bus using any of a variety of bus structures.

[0092] The electronic device can also communicate with one or more external devices (such as a keyboard, a pointing device, a Bluetooth device, etc.) and can also communicate with one or more devices that enable a user to interact with the electronic device, and / or with any devices (such as a router, a modem, etc.) that enable the electronic device to communicate with one or more other computing devices. Such communication can be carried out through an input / output (I / O) interface. In addition, the electronic device can also communicate with one or more networks (such as a local area network (LAN), a wide area network (WAN), and / or a public network, such as the Internet) through a network adapter. The network adapter communicates with other modules of the electronic device through the bus. It should be understood that although not shown in the figure, other hardware and / or software modules can be used in conjunction with the electronic device, including but not limited to: microcode, device drivers, redundant processing units, external disk drive arrays, RAID systems, tape drives, and data backup storage systems, etc.

[0093] Those skilled in the art can clearly understand, through the description of the above embodiments, that the example embodiments described herein can be implemented by software, or by software in combination with necessary hardware. Therefore, the technical solutions according to the embodiments of the present disclosure can be embodied in the form of a software product, which can be stored in a non-volatile storage medium (which can be a CD-ROM, a U disk, a mobile hard disk, etc.) or a network, and includes a plurality of instructions to enable a computing device (which can be a personal computer, a server, a terminal device, or a network device, etc.) to perform the method according to the embodiments of the present disclosure.

[0094] In the example embodiments of the present disclosure, a computer readable storage medium is also provided, which stores a program product capable of implementing the above-mentioned method of the present disclosure. In some possible embodiments, various aspects of the present disclosure can also be implemented in the form of a program product, which includes program code for causing a terminal device to perform the steps according to various example embodiments of the present disclosure described in the above-mentioned “example method” section of the present disclosure when the program product is run on the terminal device.

[0095] The program product can adopt any combination of one or more readable media. The readable medium can be a readable signal medium or a readable storage medium. The readable storage medium may, for example, be but is not limited to an electrical, magnetic, optical, electromagnetic, infrared, or semiconductor system, device or apparatus, or any combination of the above. More specific examples (non-exhaustive list) of readable storage media include an electrical connection having one or more wires, a portable disk, a hard disk, a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disk read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the above.

[0096] The computer readable signal medium can include a data signal propagated in a baseband or as a part of a carrier wave, in which readable program code is borne. Such a propagated data signal can take on multiple forms, including but not limited to an electromagnetic signal, an optical signal, or any suitable combination of the above. The readable signal medium can also be any readable medium other than the readable storage medium, which can send, propagate or transmit the program for use by or in connection with an instruction execution system, apparatus or device.

[0097] The program code contained on the readable medium can be transmitted by any suitable medium, including but not limited to wireless, wired, optical cable, RF, etc., or any suitable combination of the above.

[0098] Program code for performing the operations of the present invention can be written in any combination of one or more programming languages, including object-oriented programming languages ​​such as Java, C++, and conventional procedural programming languages ​​such as C or similar programming languages. The program code can be executed entirely on the user's computing device, partially on the user's device, as a stand-alone software package, partially on the user's computing device and partially on a remote computing device, or entirely on a remote computing device or server. In the case of a remote computing device, the remote computing device can be connected to the user's computing device via any type of network, including a local area network (LAN) or a wide area network (WAN), or can be connected to an external computing device (e.g., via the Internet using an Internet service provider).

[0099] Furthermore, the figures above are merely illustrative of the processes included in the method according to exemplary embodiments of the present invention and are not intended to be limiting. It is readily understood that the processes illustrated in the figures above do not indicate or limit the temporal order of these processes. Furthermore, it is readily understood that these processes may be executed synchronously or asynchronously, for example, in multiple modules.

[0100] It should be noted that although several modules or units of the device for action execution are mentioned in the detailed description above, this division is not mandatory. In fact, according to the embodiments of the present disclosure, the features and functions of two or more modules or units described above can be concretized in one module or unit. Conversely, the features and functions of one module or unit described above can be further divided into multiple modules or units to be concretized.

[0101] The above are merely specific embodiments of the present invention, but the scope of protection of the present invention is not limited thereto. Any changes or substitutions that can be easily conceived by a person skilled in the art within the technical scope disclosed in the present invention should be included in the scope of protection of the present invention. Therefore, the scope of protection of the present invention should be based on the scope of protection of the claims.

Claims

1. A method for quantitative collection and partial component measurement of human exhaled breath, characterized by, The application is applied to a gas measuring assembly, which comprises a gas collecting pipeline and an ultrasonic flowmeter group arranged on the wall of the gas collecting pipeline, and the ultrasonic flowmeter group comprises two ultrasonic sensors; The method comprises the following steps: In a preset collection period, the transmission time T of a forward flow signal and the transmission time t of a reverse flow signal collected by the ultrasonic flowmeter group at each collection time are acquired; According to the T and t corresponding to each collection time, the fluid velocity V corresponding to each collection time is generated; V satisfies the following condition: ； Wherein, L is the distance between the two ultrasonic sensors in the ultrasonic flowmeter group, L=D / sinφ; φ is the included angle between the connecting line of the two ultrasonic sensors and the pipeline axial direction; D is the inner diameter of the gas collecting pipeline; 1 / T-1 / t is the reciprocal of a time difference, which represents the influence degree of the gas flow rate on the sound wave propagation time; the form (1 / T-1 / t) is used, even if the flow rate is very small, the influence of the flow rate can also be reflected through the reciprocal difference of the time, which can better capture the change of the flow rate in mathematics, thereby providing more stable measurement results under low flow rate conditions; According to the fluid velocity corresponding to each collection time, the collection amount W of the components of the human exhaled gas in the preset collection period is generated, and W satisfies the following condition: ； Wherein, a and b are the start time and end time of the preset period respectively; S is the cross-sectional area of the gas collecting pipeline; The gas measuring assembly further comprises a cold trap; The gas collecting pipeline is connected with the inlet of the cold trap, the outlet of the cold trap is connected with the working electrode of the sensor or the infrared light passage through a pipeline; The volume content of part of the gas components in the exhaled gas is measured through the sensor; The ultrasonic flowmeter group is arranged as two, the two ultrasonic flowmeter groups are arranged in the same region of the gas collecting pipeline, and there is an included angle between the two ultrasonic flowmeter groups; when the two ultrasonic flowmeter groups are arranged, the connecting line of the two ultrasonic sensors of one group passes through the pipeline axis, and the connecting line of the two ultrasonic sensors of the other group does not pass through the pipeline axis.

2. The method of claim 1, wherein, The method further comprises the following steps: The two ultrasonic flowmeter groups are controlled to send and receive signals at the same collection frequency, wherein each time the ultrasonic wave signal is sent, the ultrasonic sensors at different positions in the two ultrasonic flowmeter groups are respectively used as the transmitting end; According to the T and t respectively acquired by the two ultrasonic flowmeter groups at each collection time, the fluid velocities V1 and V2 respectively corresponding to each collection time in the two ultrasonic flowmeter groups are generated; According to V1 and V2, the collection amount W of the components of the human exhaled gas in the preset collection period is generated, and W satisfies the following condition: 。 3. The method of claim 1, wherein, Before generating the collection amount W of the components of the human exhaled gas in the preset collection period according to V1 and V2, the method further comprises the following steps: If |V1-V2|>Y1, a preset alarm information is generated.

4. The method of claim 2, wherein, The gas measuring assembly further comprises a calibration flowmeter group, which has the same structure as the ultrasonic flowmeter group, and is arranged in the downstream region of the ultrasonic flowmeter group; Before generating the collection amount W of the components of the human exhaled gas in the preset collection period according to V1 and V2, the method further comprises the following steps: If |V1-V2|>Y1 at the current acquisition time, V1 and V2 are both retained; acquire T 1 z and T 2 z respectively, and check the fluid velocities V3 and V4 collected at the check flowmeter group; wherein T 1 z is the time corresponding to the current collection time plus L1 / V1; T 2 z is the time corresponding to the current collection time plus L1 / V2; and L1 is the distance between the check flowmeter group and the ultrasonic flowmeter group in the axial direction of the gas collection pipeline. If |V3-V1|<Y2, V1 is determined as the fluid velocity corresponding to the current acquisition time, Y1 and Y2 are respectively a first threshold value and a second threshold value.

5. The method of claim 4, wherein, When T 1 z and T 2 z are acquired respectively, after the fluid velocities V3 and V4 collected at the flow meter group are checked, the method further comprises: If |V4-V2|<Y2, V1 is determined as the fluid velocity corresponding to the current acquisition time.

6. The method of claim 1, wherein, The gas components in the exhaled breath include nitric oxide, carbon monoxide or carbon dioxide.

7. The method of claim 6, wherein, The temperature of the cooling surface inside the cold trap is -5℃ to -35℃.

8. The method of claim 6, wherein, The length of the pipe extending into the cold trap at the inlet is greater than the length of the pipe extending into the cold trap at the outlet. 9.A non-transitory computer-readable storage medium storing a computer program, the computer program comprising instructions causing a processor to perform the method according to any one of claims 1 to 8. The computer program, when executed by a processor, implements the method for quantitative collection of human exhaled breath and measurement of partial components according to any one of claims 1 to 8.

10. An electronic device comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, characterized in that, The processor, when executing the computer program, implements the method for quantitative collection of human exhaled breath and measurement of partial components according to any one of claims 1 to 8.

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