Respiratory Monitoring Data Correction Method, Device, Equipment and Storage Medium

Abstract

An embodiment of the present application discloses a method for correcting respiratory monitoring data, a device for correcting respiratory monitoring data, a computer device, and a computer-readable storage medium. The method includes: obtaining first respiratory data and second respiratory data, where the first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle; performing a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition; correcting the second respiratory data according to the respiratory delay to obtain third respiratory data; generating a volumetric capnogram according to the third respiratory data to determine a first airway dead space and a second airway dead space, where the first airway dead space is determined by the volumetric capnogram, and the second airway dead space is determined by the corrected volumetric capnogram; determining the airway dead space according to the first airway dead space and the second airway dead space; and outputting the airway dead space and the third respiratory data. In this way, accurate respiratory monitoring data can be obtained.

Description

Technical Field

[0001] This application belongs to the field of medical technology, and particularly relates to a method for correcting respiratory monitoring data, a device for correcting respiratory monitoring data, a computer device, and a computer-readable storage medium. Background Art

[0002] Carbon dioxide (CO2) is the gas produced most by the human body. Monitoring CO2 can reflect the metabolic, ventilation, and circulatory status of patients, and is one of the very important indicators for detecting the respiratory status of patients, having a warning function for diseases such as hypercapnia and pulmonary embolism. Therefore, CO2 monitoring has very important significance in clinical practice. Currently, there are mainly two monitoring methods: one is to observe the change law of CO2 concentration over time, but this kind of monitoring is more of a semi-quantitative monitoring, not very accurate, and is easily affected by external interference, resulting in measurement errors. The other is to observe the change law of CO2 concentration with tidal volume. The curve drawn according to the change of CO2 concentration with tidal volume is called a volume-CO2 curve graph. The analysis of the volume-CO2 curve graph has many advantages, such as: being able to improve and simplify the monitoring of patients related to metabolism, ventilation, and circulation; having multiple clinical applications, and can monitor diseases such as pulmonary embolism, hemorrhagic shock, and alveolar derecruitment; providing information related to the homogeneity or heterogeneity of the lungs, etc. In addition, airway dead space (Vdaw) is an important indicator reflecting respiratory pathophysiology, and the calculation of many parameters is further calculated based on Vdaw. Therefore, the accurate calculation of airway dead space is very important for analyzing the patient's state using the volume-CO2 curve graph.

[0003] However, due to the influence of the sensor, on the one hand, the flow rate data (Flow) and CO2 concentration data collected by the instrument are not completely matched in the respiratory phase of Flow and CO2, which will cause the tidal volume of inhalation and exhalation not to be always equal; on the other hand, CO2 will not instantaneously drop to 0 when changing from the expiratory phase to the inspiratory phase, so the tidal volume during the inhalation process is not always 0, which results in the calculated result of the CO2 volume being lower than expected. How to make up for the above technical defects is a technical problem that needs to be solved urgently by those skilled in the art.

[0004] The foregoing description is to provide general background information and does not necessarily constitute prior art. Summary of the Invention

[0005] Based on this, in view of the above problems, it is necessary to propose a method for correcting respiratory monitoring data, a device for correcting respiratory monitoring data, a computer device, and a computer-readable storage medium, which can effectively correct the monitoring data of the ventilator.

[0006] The technical problems solved by this application are achieved by adopting the following technical solutions:

[0007] The present application provides a method for correcting respiratory monitoring data, including the following steps: obtaining first respiratory data and second respiratory data, where the first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle; performing a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition; correcting the second respiratory data according to the respiratory delay to obtain third respiratory data; generating a volumetric capnogram based on the third respiratory data to determine a first airway dead space and a second airway dead space, where the first airway dead space is determined by the volumetric capnogram, and the second airway dead space is determined by the corrected volumetric capnogram; determining the airway dead space according to the first airway dead space and the second airway dead space; and outputting the airway dead space and the third respiratory data.

[0008] In an optional embodiment of the present application, performing a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition includes: performing a first delay process on the first respiratory data to determine a first respiratory delay; and performing a second delay process on the first respiratory delay to determine the respiratory delay.

[0009] In an optional embodiment of the present application, performing a first delay process on the first respiratory data to determine a first respiratory delay includes: taking a plurality of first delays with different time lengths from a coarse screening interval; respectively obtaining a plurality of tidal volume differences according to the first respiratory data and the plurality of first delays; and taking the first delay corresponding to the tidal volume difference with the smallest value as the first respiratory delay.

[0010] In an optional embodiment of the present application, performing a second delay process on the first respiratory delay to determine the respiratory delay includes: setting a fine screening interval according to the first respiratory delay, and taking a plurality of second delays with different time lengths from within the fine screening interval; respectively obtaining a plurality of tidal volume differences according to the first respiratory data and the plurality of second delays; and taking the second delay corresponding to the tidal volume difference with the smallest value as the respiratory delay.

[0011] In an alternative embodiment of the present application, the third respiratory data includes a carbon dioxide concentration value and a tidal volume; generating a volumetric carbon dioxide graph based on the third respiratory data to determine a first airway dead space, including: plotting a volumetric carbon dioxide graph according to the carbon dioxide concentration value and the tidal volume, where the X-axis of the volumetric carbon dioxide graph is the tidal volume and the Y-axis is the carbon dioxide concentration value; the volumetric carbon dioxide graph further includes a variation curve, and the variation curve characterizes the correlation between the carbon dioxide concentration value and the tidal volume; drawing a first tangent on the upper edge of the variation curve, and drawing a perpendicular line on the X-axis of the volumetric carbon dioxide graph, setting the area enclosed by the first tangent, the variation curve and the perpendicular line as the first area, and the area enclosed by the X-axis of the volumetric carbon dioxide graph, the variation curve and the perpendicular line as the second area; horizontally translating the perpendicular line until the first area is equal to the second area; taking the tidal volume of the perpendicular line and the X-axis of the volumetric carbon dioxide graph at this time as the first airway dead space.

[0012] In an alternative embodiment of the present application, generating a volumetric carbon dioxide graph based on the third respiratory data to determine a second airway dead space, including: drawing a second tangent on the rising edge of the variation curve, setting the area enclosed by the first tangent, the second tangent and the perpendicular line as the third area, and the area enclosed by the X-axis of the volumetric carbon dioxide graph, the second tangent and the perpendicular line as the fourth area; horizontally translating the perpendicular line until the third area is equal to the fourth area; taking the tidal volume of the perpendicular line and the X-axis of the volumetric carbon dioxide graph at this time as the second airway dead space.

[0013] In an alternative embodiment of the present application, determining the airway dead space according to the first airway dead space and the second airway dead space, including: obtaining a fixed coefficient, and correcting the first airway dead space and the second airway dead space through the fixed coefficient to obtain the airway dead space.

[0014] The present application also provides a respiratory monitoring data correction device, including: a delay calibration module, configured to obtain first respiratory data and second respiratory data, where the first respiratory data is respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is respiratory data collected during the current respiratory cycle; performing a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition; a first correction module, configured to correct the second respiratory data according to the respiratory delay to obtain third respiratory data; a second correction module, configured to generate a volumetric carbon dioxide graph according to the third respiratory data to determine a first airway dead space and a second airway dead space, the first airway dead space is determined by the volumetric carbon dioxide graph, and the second airway dead space is determined by the corrected volumetric carbon dioxide graph; determining the airway dead space according to the first airway dead space and the second airway dead space; an output module, configured to output the airway dead space and the third respiratory data.

[0015] The present application also provides a computer device, including a processor and a memory: the processor is configured to execute a computer program stored in the memory to implement the method as described above.

[0016] The present application also provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the method as described above.

[0017] Adopting the embodiments of the present application has the following beneficial effects:

[0018] The present application can determine the respiratory delay indicated by the current cycle from multiple cycles to correct the original respiratory data to obtain accurate respiratory data; further, multiple airway dead space algorithms are used to obtain multiple airway dead spaces and correct each other, and finally, respiratory monitoring data with more accurate calculation results and stronger anti-interference ability is output.

[0019] The above description is only an overview of the technical solution of the present application. In order to understand the technical means of the present application more clearly, it can be implemented according to the content of the specification. In order to make the above and other purposes, features and advantages of the present application more obvious and understandable, the following preferred embodiments are specifically given and described in detail in conjunction with the accompanying drawings. It should be understood that the above general description and the following detailed description are only exemplary and explanatory, and cannot limit the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the following will briefly introduce the drawings required for the description of the embodiments or the prior art. Obviously, the following drawings are only some embodiments of the present application. For those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative efforts.

[0021] Among them:

[0022] Figure 1 It is a schematic flow chart of a method for correcting respiratory monitoring data provided by an embodiment;

[0023] Figure 2 It is a volumetric carbon dioxide graph drawn when determining the first airway dead space provided by an embodiment;

[0024] Figure 3 It is a volumetric carbon dioxide graph drawn when determining the second airway dead space provided by an embodiment;

[0025] Figure 4 It is a schematic structural diagram of a device for correcting respiratory monitoring data provided by an embodiment;

[0026] Figure 5 It is an internal structure diagram of a computer device provided by an embodiment. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0027] Next, the technical solutions in the embodiments of the present application will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present application. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without making creative efforts shall fall within the protection scope of the present application.

[0028] Due to the influence of the sensor, there is a problem that the respiratory phases of the flow rate data (Flow) and carbon dioxide (hereinafter referred to as CO2) concentration data in the respiratory data collected by the respiratory monitoring instrument do not match, resulting in incorrect calculation results. The basic calculation formula for the volume of CO2 during the breathing process is as follows:

[0029]

[0030]

[0031] Among them, VeCO2 represents the tidal volume during exhalation, ViCO2 represents the tidal volume during inhalation, t1 to t2 represent the exhalation process, t3 to t4 represent the inhalation process, and represents the variation relationship of Flow and CO2 concentration with time. Therefore, the tidal volume (VCO2) of a single breath is:

[0032] VCO2 = VeCO2 - ViCO2 (3)

[0033] Theoretically, ViCO2 during inhalation should be constantly 0. However, on the one hand, due to the incomplete matching of the respiratory phases of the Flow and CO2 concentration data, this will cause VeCO2 and ViCO2 not to be always equal; on the other hand, the CO2 concentration data will not instantaneously drop to 0 when changing from the expiratory phase to the inspiratory phase, so ViCO2 is not always 0, which results in the calculated result of VCO2 being lower than expected. How to correct the defects in the respiratory monitoring data to make the calculation results more accurate and have stronger anti-interference ability proposes a method for correcting respiratory monitoring data in the present application, including steps S110 to S140. To clearly describe a method for correcting respiratory monitoring data provided in this embodiment, please refer to Figures 1 to 3 .

[0034] Step S110: Obtain first respiratory data and second respiratory data. The first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle; perform a delay process on the first respiratory data to obtain a respiratory delay that meets the preset conditions.

[0035] In one embodiment, step S110: performing a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition, including: performing a first delay process on the first respiratory data to determine a first respiratory delay; performing a second delay process on the first respiratory delay to determine the respiratory delay.

[0036] In one embodiment, performing a first delay process on the first respiratory data to determine a first respiratory delay includes: taking a plurality of first delays with different time lengths from a coarse screening interval; respectively obtaining a plurality of tidal volume differences according to the first respiratory data and the plurality of first delays; taking the first delay corresponding to the smallest tidal volume difference value as the first respiratory delay.

[0037] In one embodiment, performing a second delay process on the first respiratory delay to determine the respiratory delay includes: setting a fine screening interval according to the first respiratory delay, and taking a plurality of second delays with different time lengths from the fine screening interval; respectively obtaining a plurality of tidal volume differences according to the first respiratory data and the plurality of second delays; taking the second delay corresponding to the smallest tidal volume difference value as the respiratory delay.

[0038] In one embodiment, first, how to adjust the breathing phases of Flow and CO2 in the respiratory data to make the delay more matched to correct the VCO2 calculation result. The main idea is to take the change in the breathing phase of CO2 as the reference and adjust the delay of Flow, using the difference in tidal volume between exhalation and inhalation as the criterion for judging the delay effect. Based on this, two types of respiratory data can be obtained first, the first respiratory data and the second respiratory data, where the first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle. The respiratory data includes the aforementioned Flow and CO2 data, and the CO2 data is also the VeCO2 and ViCO2 of each cycle. For the first respiratory data, in a preferred embodiment, the respiratory data of the first two respiratory cycles can be taken. Then, a first delay process is performed on the first respiratory data, and a plurality of first delays with different time lengths are taken from the coarse screening interval to perform different degrees of time delay on the first respiratory data. Among them, the coarse screening interval is a preset data set, which includes a plurality of first delays with different values, and there can be an equal interval between the plurality of first delays. For example, the coarse screening interval can be [1s, 2s, 3s, 4s, 5s], and any one or more of the time lengths are taken as the first delay. Calculate the tidal volumes of the exhalation process and the inhalation process of the first respiratory data after each first delay respectively, and the difference between the tidal volumes of the exhalation process and the inhalation process is also the tidal volume difference. Perform time delay on the first respiratory data according to the plurality of first delays respectively, and finally obtain a plurality of tidal volume differences respectively. Since the tidal volume difference should be 0 ideally, the first delay corresponding to the smallest tidal volume difference value can be selected for further fine screening. That is, the first delay is used as the first respiratory delay TDelay , perform further fine screening.

[0039] In one embodiment, assuming that T determined above Delay is 2 s, then a fine screening interval can be set based on T Delay . The fine screening interval can be set with a certain time length before and after T Delay , for example, within 0.8 s before and after, and multiple second delays are set at intervals of 0.2 s. The fine screening interval can be expressed as [T Delay - 0.8 s, T Delay + 0.8 s], and specifically can include [1.2 s, 1.4 s, 1.6 s, 1.8 s, 2 s, 2.2 s, 2.4 s, 2.6 s, 2.8 s]. Calculate the tidal volume difference after time delay for the first respiratory data from multiple second delays with different time lengths. In a preferred embodiment, the tidal volume differences corresponding to all second delays can be taken. Similarly, determine the minimum value among the tidal volume differences corresponding to multiple second delays, and use the second delay corresponding to the minimum tidal volume difference as the finally selected respiratory delay T D . Correct the second respiratory data according to this respiratory delay, and the obtained tidal volume difference is 0 or closest to 0, which is the most ideal situation.

[0040] Step S120: Correct the second respiratory data according to the respiratory delay to obtain the third respiratory data.

[0041] In one embodiment, generally, when using a certain fixed gas monitoring module with a certain fixed adapter, the delay caused by the sensor is fixed, and T D can be used to correct the obtained respiratory data during subsequent detection. However, just in case, in a preferred embodiment, T D can also be subjected to a second delay process for correction during each subsequent respiratory cycle to ensure that the respiratory data of each respiratory cycle is accurate. When specifically performing the second delay process on T D , it can be different from the detailed adjustment described above and can be a rough screening. For example, the expiratory and inspiratory tidal volumes in three delay states of T D - 0.2 s, T D , and T D + 0.2 s can be calculated and the result with the smallest difference is selected as the delay suitable for this breath. And use the most suitable T DThe second respiratory data is corrected to obtain third respiratory data with more accurate calculation results and stronger anti-interference ability, where the content carried by the third respiratory data is the same as that of the first respiratory data and the second respiratory data. It can be understood that the numerical values exemplified above are specific descriptions of the solution and are not limitations of the solution, and can be adjusted arbitrarily according to requirements in actual situations.

[0042] Step S130: Generate a volumetric carbon dioxide graph based on the third respiratory data to determine the first airway dead space and the second airway dead space. The first airway dead space is determined by the volumetric carbon dioxide graph, and the second airway dead space is determined by the corrected volumetric carbon dioxide graph; Determine the airway dead space based on the first airway dead space and the second airway dead space.

[0043] In one embodiment, the third respiratory data includes a carbon dioxide concentration value and a respiratory tidal volume; Step S130: Generate a volumetric carbon dioxide graph based on the third respiratory data to determine the first airway dead space, including: Drawing a volumetric carbon dioxide graph based on the carbon dioxide concentration value and the respiratory tidal volume. The X-axis of the volumetric carbon dioxide graph is the respiratory tidal volume, and the Y-axis is the carbon dioxide concentration value; The volumetric carbon dioxide graph also includes a change curve, and the change curve characterizes the correlation between the carbon dioxide concentration value and the respiratory tidal volume; Draw a first tangent on the upper edge of the change curve, and draw a vertical line on the X-axis of the volumetric carbon dioxide graph. Set the area enclosed by the first tangent, the change curve, and the vertical line as the first area, and the area enclosed by the X-axis of the volumetric carbon dioxide graph, the change curve, and the vertical line as the second area; Translate the vertical line left and right until the first area is equal to the second area; Take the respiratory tidal volume of the vertical line and the X-axis of the volumetric carbon dioxide graph at this time as the first airway dead space.

[0044] In one embodiment, after determining the third respiratory data according to the foregoing, the accurate airway dead space (Airway Dead Space, Vdaw) can be calculated again. In this application, different methods can be used to calculate Vdaw and be used as corrections for each other. Specifically, a volumetric carbon dioxide graph is drawn based on the carbon dioxide concentration value and the respiratory tidal volume. The X-axis of the volumetric carbon dioxide graph is the respiratory tidal volume, and the Y-axis is the carbon dioxide concentration value. The graph also includes a change curve l c , the change curve l c characterizes the correlation between the carbon dioxide concentration value and the respiratory tidal volume. Then draw a first tangent l1 on the upper edge of the change curve l c , and draw a vertical line l v on the X-axis of the volumetric carbon dioxide graph. For the drawn image, reference can be made to Figure 2 , Figure 2 is the volumetric carbon dioxide graph drawn when determining the first airway dead space provided for an embodiment. It can be seen from Figure 2 that the first tangent l1, the change curve l c and the vertical line lv Enclose a figure p, and set the area of p as the first area; at the same time, for the volumetric carbon dioxide diagram on the X-axis and the change curve l c and the perpendicular line l v Similarly enclose to form a figure q, and set the area of q as the second area. Adjust the perpendicular line l left and right v At the intersection point with the X-axis of the volumetric carbon dioxide diagram, the sizes of the first area and the second area can be changed. When the first area is equal to the second area, the perpendicular line l v At the intersection point with the X-axis of the volumetric carbon dioxide diagram, that is, the exhaled tidal volume is the first airway dead space Vdaw1.

[0045] In one embodiment, step S130: Generate a volumetric carbon dioxide diagram according to the third respiratory data to determine the second airway dead space, including: Draw a second tangent on the rising edge of the change curve, and set the area enclosed by the first tangent, the second tangent and the perpendicular line as the third area, and the area enclosed by the X-axis of the volumetric carbon dioxide diagram, the second tangent and the perpendicular line as the fourth area; Translate the perpendicular line left and right until the third area is equal to the fourth area; Take the respiratory tidal volume at the intersection of the perpendicular line and the X-axis of the volumetric carbon dioxide diagram at this time as the second airway dead space.

[0046] In one embodiment, for the second airway dead space Vdaw2, the steps for referring to the first airway dead space Vdaw1 can be executed, where when generating the volumetric carbon dioxide diagram, a second tangent line l2 is fitted by tangency on the rising edge of the change curve l c . For the volumetric carbon dioxide diagram drawn when determining the second airway dead space, reference can be made to Figure 3 . As Figure 3 shown, the first tangent line l1, the second tangent line l2 and the perpendicular line l v enclose a figure p m , and set the area of p m as the third area; Similarly, the X-axis of the volumetric carbon dioxide diagram, the second tangent line l2 and the perpendicular line perpendicular line l v enclose to form a figure q m , and set the area of q m as the fourth area. Adjust the perpendicular line l left and right v At the intersection point with the X-axis of the volumetric carbon dioxide diagram, the sizes of the third area and the fourth area can be changed. When the third area is equal to the fourth area, the perpendicular line l v At the intersection point with the X-axis of the volumetric carbon dioxide diagram, that is, the exhaled tidal volume is the second airway dead space Vdaw2.

[0047] In one embodiment, step S130: Determine the airway dead space according to the first airway dead space and the second airway dead space, including: Obtain a fixed coefficient, and correct the first airway dead space and the second airway dead space through the fixed coefficient to obtain the airway dead space.

[0048] In one embodiment, fixed coefficients are obtained, and according to the degree of baseline offset, the first airway dead space and the second airway dead space are corrected to finally determine the airway dead space Vdaw. The degree of baseline offset can be determined by a set threshold value "threshold". The degree of baseline offset can be determined simultaneously when obtaining respiratory data based on data, experience, etc. The obtaining process will not be elaborated here. The correction process can be carried out by the following formula:

[0049]

[0050] In the formula, a, b, c, and d are all preset fixed coefficients, and their relationship can be expressed as (a + b) = 1 and a > b, (c + d) = 1 and c > d. Through experiments, after the above correction, the Vdaw of normal subjects can be closer to the theoretical value of 2.2 L / Kg, and it has good anti-interference ability, and the baseline offset will not cause large deviations in the calculation results.

[0051] Step S140: Output the airway dead space and the third respiratory data.

[0052] In one embodiment, after the above correction, the corrected airway dead space Vdaw and the third respiratory data can be output. For the third respiratory data, preferably, it can be the volume of exhaled CO2. To more accurately reflect the patient's respiratory state and play a good warning role for diseases such as hypercapnia and pulmonary embolism. In other embodiments, it is also possible to display the volumetric carbon dioxide map generated during the correction process, so as to improve and simplify the patient monitoring related to metabolism, ventilation, and circulation; it has multiple clinical applications and can monitor diseases such as pulmonary embolism, hemorrhagic shock, and alveolar derecruitment; provide information related to the homogeneity or heterogeneity of the lungs, etc., and accurately reflect the patient's state.

[0053] Therefore, this application can determine the respiratory delay indicated by the current cycle from multiple cycles to correct the original respiratory data to obtain accurate respiratory data; further, use multiple airway dead space algorithms to obtain multiple airway dead spaces and correct each other, and finally output respiratory monitoring data with more accurate calculation results and stronger anti-interference ability.

[0054] Figure 4The structural schematic diagram of a respiratory monitoring data correction device in an embodiment is shown. The respiratory monitoring data correction device 40 includes: a delay calibration module 41, a first correction module 42, a second correction module 43, and an output module 44. The delay calibration module 41 is configured to obtain first respiratory data and second respiratory data, where the first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle; perform a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition. The first correction module 42 is configured to correct the second respiratory data according to the respiratory delay to obtain third respiratory data. The second correction module 43 is configured to generate a volumetric capnogram based on the third respiratory data to determine a first airway dead space and a second airway dead space, where the first airway dead space is determined by the volumetric capnogram, and the second airway dead space is determined by the corrected volumetric capnogram; determine the airway dead space according to the first airway dead space and the second airway dead space. The output module 44 is configured to output the airway dead space and the third respiratory data.

[0055] Figure 5 The internal structure diagram of a computer device in an embodiment is shown. The computer device may specifically be a terminal or a server. As Figure 5 shown, the computer device includes a processor, a memory, and a network interface connected through a system bus. Among them, the memory includes a non-volatile storage medium and an internal memory. The non-volatile storage medium of the computer device stores an operating system and may also store a computer program. When the computer program is executed by the processor, the processor can implement the respiratory monitoring data correction method. The internal memory may also store a computer program. When the computer program is executed by the processor, the processor can execute the respiratory monitoring data correction method. Those skilled in the art can understand that Figure 5 the structure shown in

[0056] In one embodiment, a computer device is provided, which includes a memory and a processor. The memory stores a computer program. When the computer program is executed by the processor, the processor is caused to perform the following steps: Step S110: Obtain first respiratory data and second respiratory data. The first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle; perform a delay process on the first respiratory data to obtain a respiratory delay that meets a preset condition; Step S120: Correct the second respiratory data according to the respiratory delay to obtain third respiratory data; Step S130: Generate a volumetric capnogram based on the third respiratory data to determine a first airway dead space and a second airway dead space. The first airway dead space is determined by the volumetric capnogram, and the second airway dead space is determined by the corrected volumetric capnogram; determine the airway dead space according to the first airway dead space and the second airway dead space; Step S140: Output the airway dead space and the third respiratory data.

[0057] In one embodiment, the present application also provides a computer-readable storage medium storing a computer program. When the computer program is executed by a processor, the processor is caused to perform the steps of the foregoing method.

[0058] Those of ordinary skill in the art can understand that all or part of the processes of implementing the methods in the above embodiments can be completed by instructing relevant hardware through a computer program. The program can be stored in a non-volatile computer-readable storage medium. When the program is executed, it can include the processes of the embodiments of the above methods. Among them, any reference to a memory, storage, database, or other medium used in the various embodiments provided by the present application can include non-volatile and / or volatile memories. Non-volatile memories can include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM), or flash memory. Volatile memories can include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in various forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDR SDRAM), enhanced SDRAM (ESDRAM), synchronous link (Synchlink) DRAM (SLDRAM), memory bus (Rambus) direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM), etc.

[0059] The technical features of the above embodiments can be combined arbitrarily. For the sake of concise description, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, it should be considered as the scope described in this specification.

[0060] The above-described embodiments merely represent several implementation manners of the present application. The description is relatively specific and detailed, but it should not be construed as a limitation on the patent scope of the present application. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present application, several modifications and improvements can still be made, and these all belong to the protection scope of the present application. Therefore, the protection scope of the patent of the present application shall be subject to the appended claims.

Claims

1. A method for correcting respiratory monitoring data, characterized in that It includes the following steps: Obtain first respiratory data and second respiratory data, where the first respiratory data is the respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is the respiratory data collected within the current respiratory cycle; Take multiple first delays with different time lengths from the coarse screening interval; Respectively obtain multiple tidal volume differences according to the first respiratory data and the multiple first delays; Take the first delay corresponding to the tidal volume difference with the smallest value as the first respiratory delay; Perform a second delay process on the first respiratory delay to determine the respiratory delay; Correct the second respiratory data according to the respiratory delay to obtain third respiratory data; Generate a volumetric carbon dioxide graph according to the third respiratory data to determine a first airway dead space and a second airway dead space; Determine the airway dead space according to the first airway dead space and the second airway dead space; Output the airway dead space and the third respiratory data.

2. The respiratory monitoring data correction method according to claim 1, wherein The performing a second delay process on the first respiratory delay to determine the respiratory delay includes: Set a fine screening interval according to the first respiratory delay, and take multiple second delays with different time lengths from within the fine screening interval; Respectively obtain multiple tidal volume differences according to the first respiratory data and the multiple second delays; Take the second delay corresponding to the tidal volume difference with the smallest value as the respiratory delay.

3. The respiratory monitoring data correction method according to claim 1, wherein The third respiratory data includes a carbon dioxide concentration value and a respiratory tidal volume; Generating a volumetric carbon dioxide graph according to the third respiratory data to determine a first airway dead space includes: Draw the volumetric carbon dioxide graph according to the carbon dioxide concentration value and the respiratory tidal volume, where the X-axis of the volumetric carbon dioxide graph is the respiratory tidal volume and the Y-axis is the carbon dioxide concentration value; The volumetric carbon dioxide graph further includes a change curve, and the change curve characterizes the correlation between the carbon dioxide concentration value and the respiratory tidal volume; Draw a first tangent on the upper edge of the change curve, and draw a vertical line on the X-axis of the volumetric carbon dioxide graph. Set the area enclosed by the first tangent, the change curve, and the vertical line as the first area, and the area enclosed by the X-axis of the volumetric carbon dioxide graph, the change curve, and the vertical line as the second area; Translate the vertical line left and right until the first area is equal to the second area; Take the respiratory tidal volume of the vertical line and the X-axis of the volumetric carbon dioxide graph at this time as the first airway dead space.

4. The respiratory monitoring data correction method according to claim 3, wherein Generating a volumetric carbon dioxide graph according to the third respiratory data to determine a second airway dead space includes: Draw a second tangent on the rising edge of the change curve. Set the area enclosed by the first tangent, the second tangent, and the vertical line as the third area, and the area enclosed by the X-axis of the volumetric carbon dioxide graph, the second tangent, and the vertical line as the fourth area; Translate the vertical line left and right until the third area is equal to the fourth area; Take the respiratory tidal volume of the vertical line and the X-axis of the volumetric carbon dioxide graph at this time as the second airway dead space.

5. The respiratory monitoring data correction method according to claim 1, characterized in that, The determining the airway dead space according to the first airway dead space and the second airway dead space includes: Obtain a fixed coefficient, and correct the first airway dead space and the second airway dead space by the fixed coefficient to obtain the airway dead space.

6. A breathing monitoring data correction device, characterized in that, It includes: A delay calibration module, configured to obtain first respiratory data and second respiratory data, where the first respiratory data is respiratory data collected in multiple cycles before the current respiratory cycle, and the second respiratory data is respiratory data collected within the current respiratory cycle; take multiple first delays with different time lengths from the coarse screening interval; Respectively obtain multiple tidal volume differences according to the first respiratory data and the multiple first delays; take the first delay corresponding to the tidal volume difference with the smallest value as the first respiratory delay; Perform a second delay process on the first respiratory delay to determine the respiratory delay; A first correction module, configured to correct the second respiratory data according to the respiratory delay to obtain third respiratory data; A second correction module, configured to generate a volumetric carbon dioxide map according to the third respiratory data to determine a first airway dead space and a second airway dead space; determine the airway dead space according to the first airway dead space and the second airway dead space; An output module, configured to output the airway dead space and the third respiratory data.

7. A computer device, characterized in that, It includes a processor and a memory; The processor is configured to execute a computer program stored in the memory to implement the method according to any one of claims 1 to 5.

8. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores a computer program, and when the computer program is executed by the processor, it implements the method according to any one of claims 1 to 5.

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