Cumulative exhalation detection method and system based on information fusion

Abstract

The application discloses a cumulative exhalation detection method and system based on information fusion, relates to the technical field of medical detection, and is characterized in that the concentration of biomarkers in an exhaled air sample collection area is improved by using a cumulative method, and then the detection data of multiple sensors are fused to realize the detection of the concentration of exhaled air biomarkers. Unlike a traditional exhalation detection method, the application uses a mask provided with sensors as a carrier for implementing detection, and when the concentration of biomarkers in the exhaled air sample collection area of the mask reaches a balanced state, the system can calculate a detection result based on the monitoring data of the sensors and in combination with a corresponding algorithm, so that a strict and complex operation is not needed in the whole detection process, the exhalation detection operation process is greatly simplified, and a user can independently complete the detection of exhaled air biomarkers, which is very convenient.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical detection, in particular to a cumulative breath detection method and system based on information fusion. BACKGROUND

[0002] The exhaled gas contains endogenous inorganic gas and trace volatile organic compounds (VOCs) produced by metabolism, which are closely related to human physiological metabolism, disease occurrence and development, and can be used as breath biomarkers for breath analysis to achieve non-invasive diagnosis of clinical diseases. For example, the concentration of endogenous acetone in breath is positively correlated with the concentration of blood glucose in the body, which has become one of the breath biomarkers for the diagnosis of diabetes, the concentration of NO is a marker for the preliminary diagnosis of lung diseases such as asthma, and aldehyde components are related to tumor conditions, such as formaldehyde and acetaldehyde, which are breath biomarkers for lung cancer and breast cancer, respectively. In recent years, the application of breath diagnosis in the clinic has been continuously expanding, such as C13 / C14 labeled urea breath test for Helicobacter pylori infection, NO breath test for inflammation, etc. The detection of breath biomarkers in the prior art is almost in the form of single determination. In order to reduce interference errors, most of the operation processes have strict regulations (for example, the Helicobacter pylori breath test needs to be performed on an empty stomach, and for C13 breath test, the patient is required to breathe normally first, hold his breath for ten seconds, exhale the first half of the gas, blow the second half of the gas into the bag, cover it, then take a C13 urea capsule, wait for 30 minutes, and then repeat the above actions. For C14 breath test, a C14 urea capsule is first taken, and after waiting for 30 minutes, the gas is blown into the gas collection card smoothly and slowly for one to three minutes until the indicator window changes color. The amount of carbon 13 or carbon 14 detected from the exhaled gas can be used to indirectly determine the activity of Helicobacter pylori in the stomach), in general, all current breath tests need to be performed under the guidance / help of professionals, and users cannot perform the detection operation independently.

[0003] Chinese patent document CN108451077A discloses a breath detection method for a mask, which obtains initial breath data of a user through a sensor assembly arranged on the mask, processes the initial breath data to obtain effective breath data, and finally determines the breath frequency and breath intensity of the user according to the effective breath data. Although this scheme can autonomously detect the breath frequency and breath intensity of the user when the user wears the mask, it cannot detect the biomarkers in the user's exhaled breath. SUMMARY

[0004] One of the purposes of the present application is to provide a cumulative breath detection method based on information fusion using a mask as a medium, to simplify the breath detection operation mode and improve the convenience of breath biomarker detection.

[0005] To achieve the above object, the cumulative exhalation detection method based on information fusion provided by the present application comprises the following steps:

[0006] 1) detecting the inhalation or exhalation flow of a user wearing a mask through a first sensor assembly;

[0007] 2) detecting the gas in the exhaled air sample collection area of the mask worn by the user through a second sensor assembly until the change value of the detected biomarker concentration is less than the set threshold value;

[0008] 3) determining the exhalation end time and inhalation or exhalation volume of each breathing cycle;

[0009] 4) calculating the exhalation biomarker concentration C in the exhaled gas of the user according to the following formula EM :

[0010] C EM = V*ΔC / (a- Q n * b / C n ) ;

[0011] wherein V is the volume of the exhaled air sample collection area calibrated in advance; ΔC is the change value of the biomarker concentration during the detection process, ΔC = C n -C0, C n is the detected biomarker concentration value at the end of the last exhalation, C0 is the background concentration value of the biomarker in the exhaled air sample collection area; Q n is the inhalation or exhalation volume of the user corresponding to the breathing cycle when the change value of the detected biomarker concentration is less than the set threshold value; a is the total inhalation or exhalation volume of the user during the detection process ; b is the sum of the detected biomarker concentration values at the end of exhalation .

[0012] In an embodiment of the present application, the exhalation end time of each breathing cycle is determined according to the change of the inhalation or exhalation volume in step 3).

[0013] In an embodiment of the present application, an independent air inlet path is configured for the mask in step 1), and the first sensor assembly is used to monitor the gas flow change in the air inlet path of the mask; in step 3), the inhalation start and end times are determined according to the gas flow change in the air inlet path, so as to obtain the inhalation volume of each breathing cycle, and the inhalation start time of the next breathing cycle is taken as the exhalation end time of the previous cycle.

[0014] In another embodiment of the present application, in step 1), an independent exhaust path is configured for the mask, and the change in gas flow in the mask exhaust path is monitored by the first sensor assembly; in step 3), the start and end times of exhalation in each breathing cycle are determined according to the change in gas flow, and the exhalation volume of each breathing cycle is obtained.

[0015] In an embodiment of the present application, in step 2), an exhaust buffer chamber is configured at the end of the exhaust path of the mask and expands larger than the exhaust path, and a filter cloth is arranged to form a barrier between the exhaust buffer chamber and the external environment, and the inner cavity of the exhaust buffer chamber is used as the exhaled breath sample collection area.

[0016] Based on the same technical concept as the above detection method, the present application also relates to a cumulative exhalation detection system, which comprises:

[0017] a mask, comprising a mask body, wherein an exhaled breath sample collection area is arranged in the mask body;

[0018] a first sensor assembly installed on the mask body, used to detect the inhalation or exhalation volume of the user in each breathing cycle after wearing the mask;

[0019] a second sensor assembly installed on the mask body, used to detect the gas in the exhaled breath sample collection area;

[0020] a data processing unit in communication connection with the first sensor assembly and the second sensor assembly, used to determine the end time of exhalation in each breathing cycle, and calculate the concentration C of the exhalation biomarker in the exhaled gas of the user in the following manner EM :

[0021] C EM = V*ΔC / (a- Q n * b / C n ) ;

[0022] wherein V is the volume of the exhaled breath sample collection area; ΔC is the change value of the biomarker concentration during the detection process, ΔC = C n -C0, C n is the detected biomarker concentration value at the end of the last exhalation, C0 is the background concentration value of the biomarker in the exhaled breath sample collection area; Q n is the inhalation or exhalation volume of the user corresponding to the breathing cycle when the change in the biomarker concentration is less than a set threshold value; a is the total inhalation or exhalation volume of the user during the detection process ; b is the sum of the detected biomarker concentration values at the end of exhalation .

[0023] In one embodiment of the present invention, the mask body is provided with a centralized air inlet duct which is independent of the exhaust path, and a one-way air inlet valve is provided in the centralized air inlet duct. The first sensor assembly is configured to monitor the changes in gas flow in the centralized air inlet duct. The monitoring point of the first sensor assembly is located on the outside of the one-way air inlet valve. The data processing unit determines the start and end time of inhalation according to the changes in gas flow in the centralized air inlet duct, and then calculates the inhalation volume of each breathing cycle.

[0024] In another embodiment of the present invention, the mask body is provided with a centralized exhaust duct independent of the air intake path, and a one-way exhaust valve is provided in the centralized exhaust duct. The first sensor assembly is configured to monitor the changes in gas flow in the centralized exhaust duct, and the monitoring point of the second sensor assembly is located on the outside of the one-way exhaust valve. The data processing unit determines the start and end time of exhalation according to the changes in gas flow in the centralized exhaust duct, and then calculates the exhaled volume of each breathing cycle.

[0025] Preferably, the end of the exhaust path of the mask is connected to an expanded exhaust buffer chamber, and the exhaust end of the exhaust buffer chamber is provided with a filter cloth for forming a barrier between its inner cavity and the external environment. The inner cavity of the exhaust buffer chamber is the exhaled air sample collection area.

[0026] Preferably, a one-way air inlet valve and a one-way exhaust valve are provided on the mask body, the mask body includes an outer layer facing the external environment side, an inner layer facing the user side and a bracket arranged between the outer layer and the inner layer, the bracket is located at the center of the mask body and includes an inner arch and an outer arch, the inner arch is fitted with the inner layer, and the outer arch is fitted with the outer layer, and a chamber serving as an exhaled air sample collection area is formed between the inner arch and the outer arch, the input end and the output end of the one-way air inlet valve are respectively located on the outside and the inside of the mask body, the input end of the one-way exhaust valve is located on the inside of the mask body, the input end of the one-way exhaust valve is communicated with the exhaled air sample collection area, and the portion of the outer layer covering the exhaled air sample collection area includes at least a breathable area constructed of breathable filter cloth.

[0027] Unlike existing detection methods, the present invention first uses multiple accumulation methods to increase the concentration of biomarkers in the exhaled breath sample collection area, and then integrates the detection data from multiple sensors to detect the concentration of exhaled biomarkers. Because the present invention uses a mask equipped with corresponding sensors as a carrier, after the user wears the mask for a period of time (biomarker concentration reaches a state of equilibrium), the system calculates the detection results based on the monitoring data of each sensor. There is no need to perform strict and complex operations during the detection process, which greatly simplifies the exhaled breath detection operation process. Based on the system provided by the present invention, users can complete the detection of exhaled biomarkers at home independently, making exhaled biomarker detection more convenient. BRIEF DESCRIPTION OF THE DRAWINGS

[0028] Figure 1 Schematic diagram of the internal structure of the mask body in the embodiment.

[0029] In the picture:

[0030] 1——Mask body 1a——Exhaled air sample collection area 1b——Centralized air inlet

[0031] 1c - outer layer 1d - inner layer 1e - bracket

[0032] 1f - centralized exhaust duct 1e1 - inner arch 1e2 - outer arch DETAILED DESCRIPTION

[0033] In order to facilitate those skilled in the art to better understand the improvements of the present invention over the prior art, the present invention is further described below with reference to the embodiments.

[0034] Example 1:

[0035] In this embodiment, the cumulative breath detection system based on information fusion is based on a mask carrier, wherein the mask includes Figure 1 The mask body 1 of the structure shown has an exhaled gas sample collection area 1a disposed therein. A first sensor assembly and a second sensor assembly (not shown in the accompanying drawings) are mounted on the mask body 1. The first sensor assembly is used to detect the flow rate of inhalation or exhalation when the user wears the mask, and the second sensor assembly is used to detect the gas within the exhaled gas sample collection area 1a. Furthermore, the system includes a data processing unit (not shown in the accompanying drawings) that is communicatively connected to the first and second sensor assemblies. The data processing unit is used to determine the end time of exhalation and the inhalation or exhalation volume of each respiratory cycle, and to calculate the concentration of exhaled biomarkers in the user's exhaled gas.

[0036] Specifically, the mask body 1 is provided with a centralized air intake duct 1b, which is independent of the exhaust path. A one-way air intake valve is provided in the centralized air intake duct 1b. The first sensor assembly is configured to monitor changes in gas flow in the centralized air intake duct 1b, with the monitoring point of the first sensor located outside the one-way air intake valve. The data processing unit determines the start and end times of inhalation based on the changes in gas flow in the centralized air intake duct, and then calculates the inhaled volume of each respiratory cycle.

[0037] During the detection process, as the user breathes, the gas flow in the concentrated air inlet channel 1b will have the following typical changes: at the beginning of inhalation, the first sensor detects that the instantaneous flow of gas in the concentrated air inlet channel 1b gradually increases from the minimum value (the minimum value of the gas flow is theoretically 0 in the absence of external environmental airflow interference), reaches a peak, and then gradually decreases and returns to the minimum value again. During the inhalation-exhalation gap, the instantaneous flow of gas in the concentrated air inlet channel 1b remains at the minimum value. At the beginning of exhalation, since the concentrated air inlet channel 1b is independent of the exhaust path and does not interfere with each other, theoretically, the exhalation process will not affect the instantaneous flow of gas in the concentrated air inlet channel 1b. Through the above analysis, it can be known that the inhalation process corresponds to the stage in which the instantaneous flow of gas in the concentrated air inlet channel 1b gradually increases from the minimum value (inhalation start time) and then returns to the minimum value (inhalation end time). The data processing unit calculates the total gas flow in this stage to obtain the inhalation volume corresponding to the breathing cycle, and the inhalation start time of the next breathing cycle is taken as the exhalation end time of the previous cycle.

[0038] In addition, in the present embodiment, it is first assumed that the inhalation volume and the exhalation volume in the same breathing cycle are equivalent, and the second sensor assembly continuously detects the gas in the exhaled air sample collection area 1a during the detection process until the detected biomarker concentration changes by less than the set threshold value from the previous time. Considering that it is impossible for all exhaled gas to enter and remain in the exhaled air sample collection area 1a during the detection process, and in order to reduce the exhalation resistance to ensure normal breathing of the user, the gas in the exhaled air sample collection area 1a should also be able to enter the environment air through diffusion / leakage. In order to achieve the cumulative increase of the biomarker concentration, the exhaled air sample collection area 1a needs to be protected from the influence of the external airflow as much as possible. Therefore, it is necessary to set a gas-permeable airflow barrier between the exhaled air sample collection area 1a and the external environment. This barrier should ensure that the gas in the exhaled air sample collection area 1a can enter the environment air through diffusion / leakage, and must avoid being affected by the external airflow, thereby meeting the requirements of reasonable exhalation resistance and cumulative increase of biomarker concentration.

[0039] For the structure of the exhaled air sample collection area 1a, in the present embodiment, an expanded exhaust buffer chamber can be connected to the end of the exhaust path of the mask, and a filter cloth (having gas permeability but avoiding direct impact of the external airflow into the exhaust buffer chamber) is arranged at the exhaust end of the exhaust buffer chamber to form a barrier between its inner cavity and the external environment. The inner cavity of the above-mentioned exhaust buffer chamber can serve as the exhaled air sample collection area. Figure 1 One way to construct the exhaled air sample collection area 1a in the mask is shown. As shown in FIG. 1, the mask is provided with an exhaust path 1, and the exhaust path 1 is connected to the exhaled air sample collection area 1a. Figure 1As shown, the mask body 1 is provided with a one-way air inlet valve and a one-way air exhaust valve. The mask body 1 comprises an outer layer 1c facing the external environment, an inner layer 1d facing the user, and a bracket 1e disposed between the outer layer 1c and the inner layer 1d. The bracket 1e is disposed at the center of the mask body 1a and comprises an inner arch 1e1 and an outer arch 1e2. The inner arch 1e1 is bonded to the inner layer 1d, and the outer arch 1e2 is bonded to the outer layer 1c, forming a chamber between the inner arch 1e1 and the outer arch 1e2. Due to the support provided by the inner arch 1e1 and the outer arch 1e2, the size of the chamber does not change with the user's breathing during the test, thus serving as the exhaled air sample collection area 1a. To ensure that air intake and exhaust are independent of each other, the input and output ends of the one-way air intake valve are located on the outside and inside of the mask body 1a respectively, while the input end of the one-way exhaust valve is located on the inside of the mask body 1a, and the input end is connected to the exhaled breath sample collection area 1a. At the same time, the part of the outer layer 1c covering the exhaled breath sample collection area 1a (the isolation barrier between the exhaled breath sample collection area 1a and the external environment) should include at least one breathable area constructed of breathable filter cloth.

[0040] Assuming that the concentration of biomarkers in the user's exhaled gas remains stable (no statistically significant changes) during the detection process (for example, within 30 minutes), and given that the detection process will not last too long, the changes in the air permeability of the various breathable parts of the mask can also be ignored. When the mask is worn stably, it can be assumed that the leakage and diffusion of the exhaled gas sampling area 1a also remain stable. During the detection process, the second sensor component first (the first time, before the user starts to exhale) detects the background concentration of biomarkers in the exhaled gas sample collection area 1a, and then begins to detect the concentration of biomarkers in the exhaled gas sample collection area 1a during the user's breathing process. Let the background concentration of biomarkers detected for the first time be C0, and the concentration of biomarkers detected for the n+1th time be C n , then:

[0041] C n =C0+Q1*C EM / Vf*C1+Q2*C EM / V- f*C2+…+ Q n *C EM / Vf*C n (1);

[0042] In formula (1), Q is the expiratory volume corresponding to the respiratory cycle (in this embodiment, it is assumed that the respiratory volume is equivalent to the inspiratory volume, so the previously determined inspiratory volume is regarded as the expiratory volume), C EM is the biomarker concentration in the user's exhaled gas, V is the pre-calibrated volume of the exhaled gas sample collection area 1a, and f is the diffusion and leakage constant.

[0043] After adjusting the positions of the positive and negative terms in equation (1):

[0044] C n =C0+(Q1*C EM / V+Q2*C EM / V+…+Q n *C EM / V)-f*(C1+C2+…+C n )(2);

[0045] Formula (2) can be adjusted as follows:

[0046] C n =C0+ *C EM / V- f* (3);

[0047] In addition, since this embodiment stops detecting the biomarker concentration in the exhaled breath sample collection area 1a when the change in the biomarker concentration detected by the second sensor assembly compared to the previous value is less than a set threshold (equivalent to the concentration increase and diffusion leakage reaching equilibrium), in the equilibrium state, the following conditions exist:

[0048] Q n *C EM / V= f*C n (4);

[0049] Let C EM / V=C, from formula (4) we can get:

[0050] Q n *C= f*C n (5);

[0051] From formula (5), we can get:

[0052] f=Q n *C / C n (6);

[0053] make =a, =b, combining formula (6) with formula (3), we can get:

[0054] C n =C0+a*c-Q n *C * b / C n (7);

[0055] Formula (7) can be adjusted as follows:

[0056] C n =C0+(a- Q n * b / C n ) *C (8);

[0057] From equation (8), we have:

[0058] C = C n -C0) / (a- Q n * b / C n ) (9);

[0059] Further, we have:

[0060] C EM = V* (C n -C0) / (a- Q n * b / C n ) = V*ΔC / (a- Q n * b / C n ) (10);

[0061] Let C n -C0=ΔC, equation (10) can be adjusted to:

[0062] C EM = V*ΔC / (a- Q n * b / C n ) (11);

[0063] In equation (11), ΔC is the change value of the biomarker concentration during the detection process, C n is the detected biomarker concentration value at the end of the last exhalation, C0is the background concentration value of the biomarker in the exhaled gas sample collection area; Q n is the user's inhalation or exhalation volume corresponding to the respiratory cycle when the change value of the detected biomarker concentration is less than the set threshold value compared to the previous value; a is the total amount of user's inhalation or exhalation during the detection process ; b is the sum of the detected biomarker concentration values at the end of exhalation .

[0064] From the above analysis, the data processing module can calculate the exhaled biomarker concentration C EM in the user's exhaled gas based on the monitoring results of the first sensor assembly and the second sensor assembly, combined with equation (11).

[0065] Example 2:

[0066] The main difference between the present embodiment and embodiment 1 is that the mask body 1a is provided with a separate concentrated exhaust passage 1f compared to the air inlet path, and a one-way exhaust valve can also be provided in the concentrated exhaust passage 1f. In the present embodiment, the first sensor assembly is configured to monitor the change in gas flow in the concentrated exhaust passage 1f, and the monitoring point of the second sensor assembly is located on the outside of the one-way exhaust valve (on the side close to the external environment). Similar to embodiment 1, the data processing unit can determine the start and end times of exhalation according to the change in gas flow in the concentrated exhaust passage 1f (when exhaling, the change in gas flow in the concentrated exhaust passage 1f will also go through a process of gradually increasing from a minimum value, reaching a peak, and then falling back to a minimum value, and the two time points corresponding to this process are the start and end times of exhalation), and then calculate the exhalation volume of each breathing cycle.

[0067] It should be noted that, in order to ensure the fit and sealing of the mask periphery with the human face, a circle of elastic strips can be provided on the periphery of the inner layer 1a of the mask body 1, which can be made of medical silicone with a Shore hardness of 5-20 degrees, for example. This can not only ensure user comfort, but also ensure the sealing of the mask periphery, and better ensure the accuracy of the detection results. At the same time, since the mask body 1 is separately provided with a dedicated concentrated air inlet passage 1b and a concentrated exhaust passage 1f, the inner layer 1a can be made of a material that is not permeable to air (for example, a single-sided coated non-woven fabric, the side in contact with the human body is the same as ordinary non-woven fabric, has moisture absorption and skin-friendly properties, and is not prone to a stuffy feeling, and the side in contact with the inner arch 1e1 of the support 1e is the coated side), which can make the user's exhaled gas enter the exhaled gas sample collection area 1a as much as possible, then diffuse and permeate to the external environment through the exhaled gas sample collection area 1a, thereby shortening the time required for the concentration of biomarkers in the exhaled gas sample collection area 1a to balance, and improving the detection efficiency. In addition, the above first sensor assembly, second sensor assembly, and data processing unit can be detachably mounted on the mask body 1, so that the user only needs to replace the new mask body 1 for the next detection, which is beneficial to save the use cost. The above data processing unit can also be connected with the first sensor assembly and the second sensor assembly in a wireless communication manner, for example, the user's smartphone can be used as the data processing unit, and the detection data of the first sensor assembly and the second sensor assembly can be sent to the user's smartphone through a wireless communication module (such as a Bluetooth module), and the smartphone can also give the exhaled biomarker concentration detection result after processing the data in the manner mentioned above.

[0068] The biggest difference between the above embodiment and the existing breath detection method is that the concentration of the biomarker in the exhaled breath sample collection area is first increased by multiple accumulations, and then the detection data of multiple sensors are fused to realize the detection of the concentration of the breath biomarker. Since the mask with corresponding sensor components is used as the carrier, after the user wears the mask for a period of time (the concentration of the biomarker reaches a balanced state), the system can calculate the detection result based on the monitoring data of each sensor. During the entire detection process, there is no need to perform strict and complex operations, which greatly simplifies the operation process of breath detection. In this way, the user can independently complete the detection operation of the breath biomarker at home, making the breath biomarker detection more convenient.

[0069] The above embodiment is a preferred implementation scheme of the present application, in addition to this, the present application can also be implemented in other ways, any obvious replacement without departing from the technical scheme concept of the present application is within the protection scope of the present application.

[0070] In order for those skilled in the art to more conveniently understand the improvements of the present application over the prior art, some of the drawings and descriptions of the present application have been simplified, and some other elements have been omitted from the present application file for the sake of clarity, those skilled in the art should realize that these omitted elements can also constitute the content of the present application.

Claims

1. A cumulative breath test method based on information fusion, characterized in that, The method comprises the following steps: 1) detecting the inhalation or exhalation flow of a user wearing a mask through a first sensor assembly; 2) configuring the mask with an exhaust buffer chamber connected to the end of the exhaust path of the mask and larger than the exhaust path, forming a barrier between the exhaust buffer chamber and the external environment through a filter cloth, and taking the inner cavity of the exhaust buffer chamber as the exhaled air sample collection area; detecting the gas in the exhaled air sample collection area of the mask worn by the user through a second sensor assembly until the change value of the detected biomarker concentration is less than the set threshold value; 3) determining the exhalation end time and inhalation or exhalation volume of each breathing cycle; 4) The exhaled breath biomarker concentration C in the user's exhaled breath is calculated as follows EM : C EM = V* In step 3), the exhalation end time of each breathing cycle is determined according to the change of inhalation or exhalation volume. C / (a- Q n * b / C n ) ; V is the volume of the pre-calibrated breath sample collection zone; In step 1), a separate air inlet path is configured for the mask, and the first sensor assembly monitors the gas flow change in the air inlet path of the mask; in step 3), the inhalation start and end times are determined according to the gas flow change in the air inlet path, so as to obtain the inhalation volume of each breathing cycle, and the inhalation start time of the next breathing cycle is taken as the exhalation end time of the previous cycle. C is the change of biomarker concentration during the detection process, In step 1), a separate exhaust path is configured for the mask, and the first sensor assembly monitors the gas flow change in the exhaust path of the mask; in step 3), the exhalation start and end times of each breathing cycle are determined according to the gas flow change, and then the exhalation volume of each breathing cycle is obtained. C = C n -C0, C n C0 is the background concentration of the biomarker in the breath sample collection zone; Q n is the volume of the user's inhalation or exhalation in the corresponding breathing cycle when the change of the detected biomarker concentration is less than the set threshold value; a is the total volume of the user's inhalation or exhalation during the detection process ; b is the sum of the detected biomarker concentration values at the end of exhalation .

2. The cumulative exhalation test method of claim 1, wherein: It comprises:

3. The cumulative exhalation test method of claim 1, wherein: a mask comprising a mask body, wherein an exhaled air sample collection area is arranged in the mask body; an exhaust buffer chamber connected to the end of the exhaust path of the mask is arranged on the mask, wherein the exhaust end of the exhaust buffer chamber is provided with a filter cloth for forming a barrier between the inner cavity and the external environment, and the inner cavity of the exhaust buffer chamber is the exhaled air sample collection area; 4. The cumulative exhalation test method of claim 1, wherein: a first sensor assembly installed on the mask body for detecting the inhalation or exhalation flow of a user wearing a mask; 5. A cumulative breath test system based on information fusion, characterized in that, a second sensor assembly installed on the mask body for detecting the gas in the exhaled air sample collection area; The mask body is provided with a separate concentrated air inlet channel compared to the exhaust path, a one-way air inlet valve is arranged in the concentrated air inlet channel, the first sensor assembly is configured to monitor the gas flow change in the concentrated air inlet channel, the monitoring point of the first sensor assembly is located on the outside of the one-way air inlet valve, and the data processing unit determines the inhalation start and end times according to the gas flow change in the concentrated air inlet channel, and then calculates the inhalation volume of each breathing cycle. The mask body is provided with a separate concentrated exhaust channel compared to the air inlet path, a one-way exhaust valve is arranged in the concentrated exhaust channel, the first sensor assembly is configured to monitor the gas flow change in the concentrated exhaust channel, the monitoring point of the second sensor assembly is located on the outside of the one-way exhaust valve, and the data processing unit determines the exhalation start and end times according to the gas flow change in the concentrated exhaust channel, and then calculates the exhalation volume of each breathing cycle. ​ A data processing unit, in communication with the first and second sensor assemblies, is configured to determine the end of expiration time and the inspiration or expiration volume of each breath cycle, and to calculate the concentration C of the expiratory biomarker in the user's exhaled breath in the following manner EM : C EM = V* ​ C / (a- Q n * b / C n ) ; V is the volume of the exhaled breath sample collection zone; ​ C is the change in biomarker concentration during the detection process, ​ C = C n -C0, C n C0is the background concentration of the biomarker in the exhaled breath sample collection zone; Q n is the volume of the user's inhalation or exhalation during the respiratory cycle corresponding to the change in the detected biomarker concentration being less than the set threshold value; a is the total volume of the user's inhalation or exhalation during the detection process ; b is the sum of the detected biomarker concentration values at the end of exhalation .

6. The cumulative exhalation test system of claim 5, wherein: ​ 7. The cumulative exhalation test system of claim 5, wherein: ​ 8. The cumulative exhalation test system of claim 5, wherein: A one-way air inlet valve and a one-way air outlet valve are arranged on the mask body, which comprises an outer layer facing the outside environment, an inner layer facing the user, and a support arranged between the outer layer and the inner layer. The support is located at the center of the mask body and comprises an inner arch and an outer arch. The inner arch is attached to the inner layer, and the outer arch is attached to the outer layer. A cavity as an exhaled air sample collection area is formed between the inner arch and the outer arch. The input end and the output end of the one-way air inlet valve are respectively located on the outer side and the inner side of the mask body. The input end of the one-way air outlet valve is located on the inner side of the mask body. The input end of the one-way air outlet valve communicates with the exhaled air sample collection area. The outer layer covers at least a portion of the exhaled air sample collection area, which comprises a gas-permeable area formed by a gas-permeable filter cloth.

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