A method, system, device and medium for calculating the absolute end-expiratory lung volume

Abstract

The present invention discloses a method, system, device and medium for calculating the absolute end-expiratory lung volume. The method includes determining the inhalation start time point, inhalation end time point, exhalation start time point and exhalation end time point of the current user according to the detected flow rate data during a single-breath diffusion breathing test; calculating the absolute end-expiratory lung volume, which includes the first absolute end-expiratory lung volume and the second absolute end-expiratory lung volume. Since the flow rate of the test gas during the breath-holding stage can be ignored, in practice, it is not necessary to calculate the absolute end-expiratory lung volume of this part. Therefore, the method for calculating the absolute end-expiratory lung volume in the embodiments of the present invention simplifies the calculation process, reduces the calculation amount to improve the calculation efficiency, and makes the calculation of the absolute end-expiratory lung volume more appropriate and in line with the application of the actual pulmonary function test system.

Description

Technical Field

[0001] The present invention relates to the technical field of pulmonary function testing systems, and in particular, to a method, system, device, and medium for calculating the absolute end-expiratory lung volume. Background Art

[0002] A rapidly responding gas analyser (RGA Analyser) is installed in the pulmonary function testing system for performing a single-breath diffusing capacity test of pulmonary function in the pulmonary function testing system.

[0003] Currently, the standard "2017 ERS / ATS standards for single-breath carbon monoxide uptake in the lung" points out the calculation method of the absolute end-expiratory lung volume (Vee): the sum of the inhaled and exhaled gas volumes is the integral of the flow rate and the test gas concentration with respect to time. The calculation process includes the time from the start of inhaling the test gas, to breath-holding, and finally to exhaling the gas. Some redundant calculation processes are included in the calculation process. During the breath-holding process, the flow rate is 0 at this time, and the calculation of the breath-holding process is invalid. According to the calculation method of this standard, a large amount of gas concentration data and flow rate data need to be collected, resulting in an excessive calculation amount, making it difficult to efficiently obtain the desired parameter results. Summary of the Invention

[0004] The present invention aims to at least solve one of the technical problems existing in the prior art. For this reason, the present invention proposes a method for calculating the absolute end-expiratory lung volume, which solves the problem that the calculation of the absolute end-expiratory lung volume in the current single-breath diffusing capacity test of pulmonary function is too complex and inefficient.

[0005] The present invention also provides a system for calculating the absolute end-expiratory lung volume, an electronic device, and a computer-readable storage medium.

[0006] The method for calculating the absolute end-expiratory lung volume according to the first aspect embodiment of the present invention includes the following steps:

[0007] When performing a single-breath diffusing capacity breathing test of pulmonary function, determine the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point of the current user according to the detected flow rate data;

[0008] Calculate the absolute end-expiratory lung volume, which includes a first absolute end-expiratory lung volume and a second absolute end-expiratory lung volume. The first absolute end-expiratory lung volume is calculated based on a first time period from the start time point of inspiration to the end time point of inspiration, and the second absolute end-expiratory lung volume is calculated based on a second time period from the start time point of expiration to the end time point of expiration;

[0009] The calculation of the absolute end-expiratory lung volume includes:

[0010] The calculation method of the absolute end-expiratory lung volume according to the embodiments of the present invention has at least the following beneficial effects:

[0011] By respectively determining the start time point of inspiration, the end time point of inspiration, the start time point of expiration, and the end time point of expiration, the inspiration duration and expiration duration in the one-breath diffusion test of lung function can be determined, and the first absolute end-expiratory lung volume in the inspiration phase and the second absolute end-expiratory lung volume in the expiration phase can be calculated respectively. At the same time, since the flow rate of the test gas during the breath-holding phase can be ignored, it is not necessary to calculate the absolute end-expiratory lung volume of this part in practice. Therefore, the calculation method of the absolute end-expiratory lung volume in the embodiments of the present invention simplifies the calculation process, reduces the calculation amount to improve the calculation efficiency, and makes the calculation of the absolute end-expiratory lung volume more appropriate and in line with the application of the actual lung function test system.

[0012] According to some embodiments of the present invention, before calculating the absolute end-expiratory lung volume, the following steps are further included:

[0013] Interpolate the data with a lower sampling rate in the tracer gas concentration data and the flow rate data;

[0014] Correspondingly update the interpolated tracer gas concentration data or flow rate data to the or the for calculating the absolute end-expiratory lung volume .

[0015] According to some embodiments of the present invention, determining the start time point of inspiration includes the following steps:

[0016] At the start of inspiration in the one-breath diffusion test of lung function, obtain the first time point when the flow rate value is greater than the first flow rate threshold;

[0017] Determine the first time point as the start time point of inspiration.

[0018] According to some embodiments of the present invention, determining the end time point of inspiration includes the following steps:

[0019] During the inhalation process of the pulmonary function single-breath diffusing capacity test, obtain a second time point at which the flow value is equal to 0;

[0020] Obtain a third time point after a first preset time from the second time point;

[0021] If the flow value at the third time point is equal to 0, determine the second time point as the inhalation end time point.

[0022] According to some embodiments of the present invention, determining the inhalation end time point includes the following steps:

[0023] During the inhalation process of the pulmonary function single-breath diffusing capacity test, obtain a plurality of fourth time points at which the volume value is the largest, where the volume value represents the product of the flow value and time;

[0024] Determine the earliest time point among the plurality of fourth time points as the inhalation end time point.

[0025] According to some embodiments of the present invention, determining the exhalation start time point includes the following steps:

[0026] During the breath-holding process of the pulmonary function single-breath diffusing capacity test, obtain a plurality of fifth time points at which the volume value is the largest;

[0027] Determine the latest time point among the plurality of fifth time points as the exhalation start time point.

[0028] According to some embodiments of the present invention, determining the exhalation end time point includes the following steps:

[0029] During the exhalation process of the pulmonary function single-breath diffusing capacity test, obtain a plurality of sixth time points at which the flow value is equal to 0;

[0030] Determine the earliest time point among the plurality of sixth time points as the exhalation end time point.

[0031] According to the exhalation end absolute lung volume calculation system of the second aspect embodiment of the present invention, it includes:

[0032] A time node determination unit, configured to determine the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point of the current user according to the detected flow data when performing a single-breath diffusing respiration detection;

[0033] A calculation unit for calculating the absolute end-expiratory lung volume, which includes a first absolute end-expiratory lung volume and a second absolute end-expiratory lung volume. The first absolute end-expiratory lung volume is calculated based on a first time period from the start time point of inspiration to the end time point of inspiration, and the second absolute end-expiratory lung volume is calculated based on a second time period from the start time point of expiration to the end time point of expiration;

[0034] The calculation of the absolute end-expiratory lung volume includes: Among them, represents the start time point of inspiration; represents the end time point of inspiration; represents the start time point of expiration; represents the end time point of expiration; represents time under the tracer gas concentration data; represents the average tracer gas concentration data at the end of expiration; represents time under the flow rate data; represents the absolute end-expiratory lung volume.

[0035] The calculation system of the absolute end-expiratory lung volume according to the embodiment of the present invention has at least the following beneficial effects:

[0036] By using the time node determination unit to respectively determine the start time point of inspiration, the end time point of inspiration, the start time point of expiration, and the end time point of expiration, the inspiration duration and expiration duration in the pulmonary function single-breath diffusion test can be determined, and the calculation unit of the absolute end-expiratory lung volume is used to respectively calculate the first absolute end-expiratory lung volume in the inspiration phase and the second absolute end-expiratory lung volume in the expiration phase. At the same time, since the flow rate of the test gas during the breath-holding phase can be ignored, it is not necessary to calculate the absolute end-expiratory lung volume of this part in practice. Therefore, the calculation system of the absolute end-expiratory lung volume according to the embodiment of the present invention simplifies the calculation process, reduces the calculation amount to improve the calculation efficiency, and makes the calculation of the absolute end-expiratory lung volume more accurate and in line with the application of the actual pulmonary function test system.

[0037] An electronic device according to an embodiment of the third aspect of the present invention includes at least one control processor and a memory communicatively connected to the at least one control processor; the memory stores instructions executable by the at least one control processor, and the instructions are executed by the at least one control processor so that the at least one control processor can execute the calculation method of the absolute end-expiratory lung volume as described in the embodiment of the first aspect of the present invention.

[0038] A computer-readable storage medium according to an embodiment of the fourth aspect of the present invention, the computer-readable storage medium stores computer-executable instructions, and the computer-executable instructions are used to cause a computer to execute the method for calculating the absolute end-expiratory lung volume as described in the embodiment of the first aspect of the present invention.

[0039] It can be understood that the beneficial effects of the above-mentioned third aspect and fourth aspect compared with the related art are the same as those of the above-mentioned first aspect compared with the related art. For relevant descriptions, reference can be made to the relevant descriptions in the above-mentioned first aspect, and details will not be repeated here.

[0040] Other features and advantages of the present invention will be described in the following specification, and in part, will be obvious from the specification, or will be understood by implementing the present invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0041] The above and / or additional aspects and advantages of the present invention will become obvious and easy to understand from the description of the embodiments in conjunction with the following drawings, where:

[0042] Figure 1 is a flowchart of a method for calculating the absolute end-expiratory lung volume according to an embodiment of the present invention;

[0043] Figure 2 is a schematic diagram of the time / volume relationship during the one-breath diffusion test of lung function according to an embodiment of the present invention;

[0044] Figure 3 is a schematic diagram comparing the volume and gas concentration during the calculation of the absolute end-expiratory lung volume according to an embodiment of the present invention. EMBODIMENTS

[0045] The embodiments of the present invention will be described in detail below. Examples of the embodiments are shown in the drawings, where the same or similar reference numerals represent the same or similar elements or elements with the same or similar functions throughout. The embodiments described below with reference to the drawings are exemplary and are only used to explain the present invention and should not be construed as a limitation of the present invention.

[0046] In the description of the present invention, if the first, second, etc. are described, it is only for the purpose of distinguishing technical features and should not be construed as indicating or implying relative importance or implicitly indicating the quantity of the indicated technical features or implicitly indicating the sequence of the indicated technical features.

[0047] In the description of the present invention, it should be understood that for the orientation description, such as the orientation or positional relationship indicated by up, down, etc., it is based on the orientation or positional relationship shown in the drawings. It is only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation. Therefore, it should not be construed as a limitation to the present invention.

[0048] In the description of the present invention, it should be noted that unless otherwise clearly defined, terms such as "set", "installed", "connected", etc. should be understood in a broad sense. Those skilled in the art can reasonably determine the specific meanings of the above terms in the present invention in combination with the specific content of the technical solution.

[0049] Next, the technical solution of the present invention will be clearly and completely described in conjunction with the drawings. Obviously, the following described embodiments are part of the embodiments of the present invention, not all embodiments.

[0050] See Figure 1 As shown, it is a flowchart of a method for calculating the absolute end-expiratory lung volume provided by an embodiment of the present invention. The method includes the following steps:

[0051] S110: When performing a single-breath diffusive breathing test, determine the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point of the current user according to the detected flow data.

[0052] S120: Calculate the absolute end-expiratory lung volume. The absolute end-expiratory lung volume includes a first absolute end-expiratory lung volume and a second absolute end-expiratory lung volume. The first absolute end-expiratory lung volume is calculated according to the first time period from the inhalation start time point to the inhalation end time point, and the second absolute end-expiratory lung volume is calculated according to the second time period from the exhalation start time point to the exhalation end time point.

[0053] Calculating the absolute end-expiratory lung volume includes:

[0054] Wherein, represents the inhalation start time point; represents the inhalation end time point; represents the exhalation start time point; represents the exhalation end time point; represents time the tracer gas concentration data at; represents the average tracer gas concentration data at the end of exhalation; represents time the flow data at; represents the absolute end-expiratory lung volume.

[0055] Specifically, asFigure 1 As shown, it should be noted that according to the calculation method of the end-expiratory absolute lung volume Vee specified in the standard "2017 ERS / ATS standards for single-breath carbon monoxide uptake in the lung": the sum of the volumes of inhaled and exhaled gases / volume is an integral of flow rate and test gas concentration with respect to time, and the calculation process includes the time from the start of inhalation of the test gas, to breath-holding, and finally to exhalation of the gas. It can be understood that in practical applications, the calculation process contains some redundant calculation processes, mainly the breath-holding process. The flow rate during the breath-holding process is 0, so excessive calculation of the breath-holding process is relatively meaningless. Further, referring to Figure 2 , from Figure 2 it can be seen that the one-breath diffusion test process of lung function mainly includes the normal and uniform breathing stage, or the tidal breathing stage, then pre-exhalation to expel as much gas from the lungs as possible, and then the inhalation stage, breath-holding stage, and exhalation stage of the test gas. It can be understood that calculating the end-expiratory absolute lung volume of the one-breath diffusion test of lung function also mainly involves calculating the inhalation stage, breath-holding stage, and exhalation stage. However, according to the actual situation, the end-expiratory absolute lung volume under the breath-holding stage is no longer calculated. That is, by determining the start time point of inhalation, end time point of inhalation, start time point of exhalation, and end time point of exhalation during the one-breath diffusion test of lung function, then calculating the first end-expiratory absolute lung volume during the inhalation stage and the second end-expiratory absolute lung volume during the exhalation stage, and obtaining the final required end-expiratory absolute lung volume based on volume summation.

[0056] Furthermore, it should be noted that for the calculation method before improvement, its mathematical model constraint is:

[0057] Among them, to It represents three consecutive stages of an inhalation process, a breath-holding process, and an exhalation process, and based on this time period, the product of the tracer gas concentration data and the flow rate data is integrated over time, and finally the corresponding absolute end-expiratory lung volume is obtained. Therefore, it can be understood that the mathematical model of the embodiment of the present invention deletes the time integration of the product of the tracer gas concentration data and the flow rate data during the breath-holding process. Therefore, the beneficial effect of the embodiment of the present invention is reflected in the mathematical expression, that is, the problem of excessive calculation amount is improved according to the actual situation, and the calculation efficiency is improved. In this embodiment, by respectively determining the inhalation start time point, the inhalation end time point, the exhalation start time point, and the exhalation end time point, the inhalation duration and the exhalation duration in the pulmonary function single-breath diffusion test can be determined, and the first absolute end-expiratory lung volume in the inhalation phase and the second absolute end-expiratory lung volume in the exhalation phase can be calculated respectively. At the same time, since the flow rate of the test gas during the breath-holding phase can be ignored, there is no need to calculate the absolute end-expiratory lung volume of this part in practice. Therefore, the calculation method of the absolute end-expiratory lung volume in the embodiment of the present invention simplifies the calculation process, reduces the calculation amount to improve the calculation efficiency, and makes the calculation of the absolute end-expiratory lung volume more appropriate and in line with the application of the actual pulmonary function test system.

[0058] In some embodiments, before calculating the absolute end-expiratory lung volume, the following steps are further included:

[0059] Interpolate the data with a lower sampling rate in the tracer gas concentration data and the flow rate data;

[0060] Correspondingly update the interpolated tracer gas concentration data or flow rate data to or for calculating the absolute end-expiratory lung volume . Specifically, it should be noted first that when obtaining the collected tracer gas concentration data or flow rate data to calculate the absolute end-expiratory lung volume When there is a situation where the acquisition rates of gas concentration data and flow rate data are inconsistent, the main reasons are as follows: The detection of gas concentration data is processed by a gas sensor, while the detection of flow rate data is processed by a flow sensor. Therefore, different data detection tools are one of the reasons for the inconsistent acquisition rates. Since the gas concentration data and the flow rate data are respectively detected by the gas sensor and the flow sensor, and after detection, they will be transmitted to the calculation module of the pulmonary function test system for processing. For the data transmission process, it is generally sent to the host computer software through transmission tools such as serial ports or USBs, and finally the function of parameter calculation is realized in the host computer software. Therefore, the differences in the transmission rates of transmission tools such as serial ports or USBs are another reason for the inconsistent acquisition rates. It can be understood that for the situation where the acquisition rates of gas concentration data and flow rate data are inconsistent, in this embodiment, interpolation processing is performed on the data with the relatively smaller acquisition rate among the tracer gas concentration data and the flow rate data. Specific interpolation methods can adopt Lagrange interpolation method, average value method, etc. After interpolation processing, the data volumes of the flow rate data and the gas concentration data are ensured to be consistent in time, thereby reducing the calculation error and improving the accuracy of the calculation result.

[0061] Furthermore, for the embodiments of the present invention, assuming that the inhalation process of a pulmonary function single-breath diffusion test is 2 seconds, the breath-holding process is 10 seconds, and the exhalation process is 2 seconds. According to the flow rate data acquisition rate of 1000 per second and the gas concentration data acquisition rate of 500 per second, according to the unimproved calculation method, the data that needs to be calculated more during the breath-holding process is 10,000. And using the calculation method of the embodiments of the present invention, interpolation is performed on the gas concentration data during the inhalation process and the exhalation process respectively, and 1000 gas data are interpolated respectively. In the overall calculation, the total data volume is reduced by 8000 data, so the calculation amount is simplified to a large extent and the calculation efficiency is improved. In some embodiments, as Figure 3 shown, to determine the inhalation start time point, the following steps are included:

[0062] At the start of inhalation in a pulmonary function single-breath diffusion test, obtain the first time point when the flow rate value is greater than the first flow rate threshold;

[0063] Determine the first time point as the inhalation start time point.

[0064] Specifically, refer to Figure 3, it should be noted that before the start of inspiration in the one - breath diffusion test of lung function, pre - expiration is required. Since the measured flow rate is very small but the time occupied is very long after pre - expiration and before the start of inspiration, the determined start time point of inspiration will be too early. Therefore, in this embodiment, according to this situation, a first flow rate threshold is set. When the flow rate value first exceeds the first flow rate threshold starting from 0, the current time point, that is, the first time point, is obtained, and this first time point is determined as the start time point of inspiration. For details, reference can be made to Figure 3 the start time point of inspiration in .

[0065] In some embodiments, as Figure 3 shown, determining the end time point of inspiration includes the following steps:

[0066] During the inspiration process of the one - breath diffusion test of lung function, obtain the second time point when the flow rate value is equal to 0;

[0067] Obtain the third time point after the first preset time from the second time point;

[0068] If the flow rate value at the third time point is equal to 0, determine the second time point as the end time point of inspiration.

[0069] Specifically, referring to Figure 3 , it can be understood that after determining the start time point of inspiration, continuing to determine the end time point of inspiration can determine the entire time period of the inspiration process. Since the breath - holding process will start after the inspiration process and the flow rate value during the breath - holding process is 0, it can be first clear that the flow rate value at the end time point of inspiration should be 0. Further, when actually performing the one - breath diffusion test of lung function, the subject may not be able to reach the required inspiratory vital capacity in one - time inspiration, so there may be a situation of inhaling part and then continuing to inhale, that is, continuous multi - segment inspiration, which will lead to multiple time points with a flow rate value of 0 during the inspiration process. Therefore, in this embodiment, after obtaining the second time point with a flow rate value of 0, the flow rate value after a certain period of time, that is, whether the flow rate value at the third time point is still 0, is confirmed, so as to determine whether it enters the breath - holding process or is still in the inspiration process after the second time point, thus eliminating the above - mentioned mis - measurement situation. Specifically, for example, the first preset time can be set to 1 second, that is, if the flow rate value 1 second after the second time point is still 0, the second time point can be determined as the end time point of inspiration. For details, reference can be made to Figure 3 the end time point of inspiration in .

[0070] In some embodiments, as Figure 3 shown, determining the end time point of inspiration includes the following steps:

[0071] During the inhalation process of a single-breath diffusing capacity test of lung function, obtain multiple fourth time points at the maximum volume value, where the volume value represents the product of the flow value and time;

[0072] Determine the earliest time point among the multiple fourth time points as the end time point of inhalation.

[0073] Specifically, referring to Figure 3 , it can be understood that another method can also be used to determine the end time point of inhalation. Since the calculation formula for the volume value is volume = flow × time, that is, the volume value is equal to the product of the flow value and time. Therefore, based on this formula, the maximum volume value during the inhalation process can be calculated. As can be seen from Figure 3 , since the breath-holding process starts after inhalation, there are several fourth time points during this process where the volume value is at the maximum. Therefore, determine the fourth time point that reaches the maximum volume value earliest as the end time point of inhalation. It should be noted that the volume value volume in the embodiments of the present invention and the absolute lung volume at the end of exhalation are two different parameters.

[0074] In some embodiments, as shown in Figure 3 , to determine the start time point of exhalation, the following steps are included:

[0075] During the breath-holding process of a single-breath diffusing capacity test of lung function, obtain multiple fifth time points at the maximum volume value;

[0076] Determine the latest time point among the multiple fifth time points as the start time point of exhalation.

[0077] Specifically, referring to Figure 3 , it can be understood that, similarly, as can be seen from Figure 3 , since the exhalation process starts after the breath-holding process, there are several fifth time points during this process where the volume value is at the maximum. Therefore, determine the fifth time point that is the latest at the maximum volume value as the end time point of inhalation. Specifically, refer to the end time point of inhalation in Figure 3 . It can be understood that the multiple fifth time points are actually equivalent to the multiple fourth time points. The fourth and fifth are only used to distinguish different embodiments. .

[0078] In some embodiments, as shown in Figure 3 , to determine the end time point of exhalation, the following steps are included:

[0079] During the exhalation process of a single-breath diffusing capacity test of lung function, obtain multiple sixth time points when the flow value is equal to 0;

[0080] Determine the earliest time point among the multiple sixth time points as the end time point of exhalation.

[0081] Specifically, referring to Figure 3 , it can be understood that after determining the exhalation start time point, continuing to determine the exhalation end time point, the entire time period of the exhalation process can be determined. Since the flow value will always be equal to 0 after exhalation, therefore, the earliest time point can be determined from the time at one end where the flow value is equal to 0, that is, the earliest time point is determined from multiple sixth time points as the exhalation end time point. Specifically, reference can be made to Figure 3 for the inhalation end time point .

[0082] In addition, an exhaled end absolute lung volume calculation system according to an embodiment of the present invention includes: a time node determination unit and a calculation unit. The time node determination unit is used to determine the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point of the current user according to the detected flow data when performing a single-breath diffusion respiration detection; the calculation unit is used to calculate the exhaled end absolute lung volume, and the exhaled end absolute lung volume includes a first exhaled end absolute lung volume and a second exhaled end absolute lung volume. The first exhaled end absolute lung volume is calculated according to the first time period from the inhalation start time point to the inhalation end time point, and the second exhaled end absolute lung volume is calculated according to the second time period from the exhalation start time point to the exhalation end time point; calculating the exhaled end absolute lung volume includes:

[0083] Among them, represents the inhalation start time point; represents the inhalation end time point; represents the exhalation start time point; represents the exhalation end time point; represents time of the tracer gas concentration data; represents the average tracer gas concentration data at the end of exhalation; represents time of the flow data; represents the exhaled end absolute lung volume.

[0084] Specifically, referring to Figure 1, It can be understood that the calculation system of the absolute end-expiratory lung volume in the embodiments of the present application is used to implement the calculation method of the absolute end-expiratory lung volume. The calculation system of the absolute end-expiratory lung volume in the embodiments of the present application corresponds to the aforementioned calculation method of the absolute end-expiratory lung volume. For the specific processing process, please refer to the aforementioned calculation method of the absolute end-expiratory lung volume, which will not be elaborated here. In this embodiment, by using the time node determination unit, the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point are respectively determined, so that the inhalation duration and exhalation duration in the pulmonary function one-breath diffusion test can be determined. And by using the calculation unit of the absolute end-expiratory lung volume, the first absolute end-expiratory lung volume in the inhalation phase and the second absolute end-expiratory lung volume in the exhalation phase are respectively calculated. At the same time, since the test gas flow during the breath-holding phase can be ignored, in practice, it is not necessary to calculate the absolute end-expiratory lung volume of this part. Therefore, the calculation system of the absolute end-expiratory lung volume in the embodiments of the present invention simplifies the calculation process, reduces the calculation amount to improve the calculation efficiency, and makes the calculation of the absolute end-expiratory lung volume more appropriate and in line with the application of the actual pulmonary function test system.

[0085] In addition, the embodiments of the present invention further provide an electronic device, including at least one control processor and a memory for communicatively connecting with at least one control processor; the memory stores instructions executable by at least one control processor, and the instructions are executed by at least one control processor so that at least one control processor can execute the calculation method of the absolute end-expiratory lung volume as in the embodiments of the present invention.

[0086] As a non-transitory computer-readable storage medium, the memory can be used to store non-transitory software programs and non-transitory computer-executable programs. In addition, the memory may include a high-speed random access memory, and may also include a non-transitory memory, such as at least one magnetic disk storage device, a flash memory device, or other non-transitory solid-state storage devices. In some embodiments, the memory may optionally include a memory remotely set relative to the processor, and these remote memories can be connected to the processor through a network. Examples of the above networks include, but are not limited to, the Internet, an enterprise intranet, a local area network, a mobile communication network, and combinations thereof.

[0087] The non-transitory software programs and instructions required to implement the calculation method of the absolute end-expiratory lung volume in the above embodiments are stored in the memory. When executed by the processor, the calculation method of the absolute end-expiratory lung volume in the above embodiments is executed. For example, the method steps S110 to step S120 described above are executed. Figure 1 in the above.

[0088] The system embodiments described above are merely illustrative. The units described as separate components may or may not be physically separated, that is, they may be located in one place or distributed to multiple network units. Some or all of the units can be selected according to actual needs to achieve the purpose of the solution of this embodiment.

[0089] In addition, an embodiment of the present invention further provides a computer-readable storage medium storing computer-executable instructions, which are executed by one or more control processors, enabling the one or more control processors to execute a method for calculating the absolute end-expiratory lung volume in the above method embodiments. For example, execute the Figure 1 method steps S110 to S120 described above.

[0090] Those of ordinary skill in the art can understand that all or some of the steps and systems in the methods disclosed above can be implemented as software, firmware, hardware, and their appropriate combinations. Some physical components or all physical components can be implemented as software executed by a processor, such as a central processing unit, a digital signal processor, or a microprocessor, or implemented as hardware, or implemented as an integrated circuit, such as an application-specific integrated circuit. Such software can be distributed on a computer-readable medium, which can include a computer storage medium (or non-transitory medium) and a communication medium (or transitory medium). As is well known to those of ordinary skill in the art, the term computer storage medium includes volatile and non-volatile, removable and non-removable media implemented in any method or technology for storing information, such as computer-readable instructions, data structures, program modules, or other data. Computer storage media include, but are not limited to, RAM, ROM, EEPROM, flash memory, or other memory technologies, CD-ROM, digital versatile disk (DVD), or other optical disk storage, magnetic cartridges, tapes, magnetic disk storage, or other magnetic storage devices, or any other medium that can be used to store the desired information and can be accessed by a computer. In addition, as is well known to those of ordinary skill in the art, a communication medium typically includes computer-readable instructions, data structures, program modules, or other data in a modulated data signal such as a carrier wave or other transmission mechanism, and can include any information delivery medium.

[0091] The above has described the embodiments of the present invention in detail with reference to the drawings, but the present invention is not limited to the above embodiments. Within the scope of knowledge possessed by those of ordinary skill in the relevant technical field, various changes can be made without departing from the gist of the present invention.

Claims

1. A method for calculating the absolute end - expiratory lung volume, characterized in that, It includes the following steps: When performing a one - breath diffusion breathing test of lung function, determine the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point of the current user according to the detected flow rate data; Calculate the absolute end - expiratory lung volume, where the absolute end - expiratory lung volume includes a first absolute end - expiratory lung volume and a second absolute end - expiratory lung volume. The first absolute end - expiratory lung volume is calculated based on the first time period from the inhalation start time point to the inhalation end time point, and the second absolute end - expiratory lung volume is calculated based on the second time period from the exhalation start time point to the exhalation end time point; The calculation of the absolute end - expiratory lung volume includes: Among them, represents the start time point of the inhalation; represents the end time point of the inhalation; represents the start time point of the exhalation; represents the end time point of the exhalation; represents time the tracer gas concentration data at; represents the average tracer gas concentration data at the end of exhalation; represents time the flow rate data at; represents the absolute lung volume at the end of exhalation.

2. The method for calculating the absolute end - expiratory lung volume according to claim 1, characterized in that, Before calculating the absolute end - expiratory lung volume, it also includes the following steps: Interpolate the data with a lower sampling rate in the tracer gas concentration data and the flow rate data; Correspondingly update the tracer gas concentration data or flow rate data after the interpolation process to the or the for calculating the absolute end-expiratory lung volume .

3. The method for calculating the absolute end - expiratory lung volume according to claim 1, characterized in that, Determining the inhalation start time point includes the following steps: At the start of inhalation during the one - breath diffusion test of lung function, obtain the first time point when the flow rate value is greater than the first flow rate threshold; Determine the first time point as the inhalation start time point.

4. The method for calculating the absolute end - expiratory lung volume according to any one of claims 1 to 3, characterized in that, Determining the inhalation end time point includes the following steps: During the inhalation process of the one - breath diffusion test of lung function, obtain the second time point when the flow rate value is equal to 0; Obtain the third time point after a first preset time from the second time point; If the flow rate value at the third time point is equal to 0, determine the second time point as the inhalation end time point.

5. The method for calculating the absolute end - expiratory lung volume according to any one of claims 1 to 3, characterized in that, Determining the inhalation end time point includes the following steps: During the inhalation process of the one - breath diffusion test of lung function, obtain multiple fourth time points with the maximum volume value, where the volume value represents the product of the flow rate value and time; Determine the earliest time point among the multiple fourth time points as the inhalation end time point.

6. The method for calculating the absolute end - expiratory lung volume according to claim 1, characterized in that, Determining the exhalation start time point includes the following steps: During the breath - holding process of the one - breath diffusion test of lung function, obtain multiple fifth time points with the maximum volume value; Determine the latest time point among the multiple fifth time points as the exhalation start time point.

7. The method for calculating the absolute end - expiratory lung volume according to claim 1 or 6, characterized in that, Determining the exhalation end time point includes the following steps: During the exhalation process of the one - breath diffusion test of lung function, obtain multiple sixth time points when the flow rate value is equal to 0; Determine the earliest time point among the multiple sixth time points as the exhalation end time point.

8. A system for calculating the absolute end - expiratory lung volume, characterized in that, It includes: A time - node determination unit for determining the inhalation start time point, inhalation end time point, exhalation start time point, and exhalation end time point of the current user according to the detected flow rate data when performing a one - breath diffusion breathing test; A calculation unit for calculating the absolute end - expiratory lung volume, where the absolute end - expiratory lung volume includes a first absolute end - expiratory lung volume and a second absolute end - expiratory lung volume. The first absolute end - expiratory lung volume is calculated based on the first time period from the inhalation start time point to the inhalation end time point, and the second absolute end - expiratory lung volume is calculated based on the second time period from the exhalation start time point to the exhalation end time point; The calculation of the absolute end - expiratory lung volume includes: Among them, represents the start time point of inspiration; represents the end time point of inspiration; represents the start time point of expiration; represents the end time point of expiration; represents time the tracer gas concentration data at; represents the average tracer gas concentration data at the end of expiration; represents time the flow rate data at; represents the absolute lung volume at the end of expiration.

9. An electronic device, characterized in that Comprising at least one control processor and a memory communicatively connected to the at least one control processor; the memory stores instructions executable by the at least one control processor, and the instructions are executed by the at least one control processor to enable the at least one control processor to execute the method for calculating the absolute end-expiratory lung volume according to any one of claims 1 to 7.

10. A computer-readable storage medium, characterized in that The computer-readable storage medium stores computer-executable instructions for causing a computer to execute the method for calculating the absolute end-expiratory lung volume according to any one of claims 1 to 7.

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