Detection of respiratory limitation events and ventilator

Abstract

The embodiment provides a detection device of a respiratory limitation event and a breathing machine, and relates to the technical field of medical instruments.In the detection device, the second acquisition module can acquire a first inspiration period, the determination module can determine a second inspiration period, the detection module can construct a similar triangle according to the first inspiration period and the second inspiration period, the shape feature of the inspiration curve is represented by the similar area ratio of the similar triangle, and according to the theorem of the similar triangle, the similar area ratio is equal to the square of the similarity ratio of the similar triangle, so that the shape feature of the inspiration curve can be represented according to the ratio of the first inspiration period and the second inspiration period, and the device has the advantages of small operation amount, strong anti-interference and good real-time performance.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and more specifically, to a detection device and ventilator for respiratory restriction events. Background Technology

[0002] Flow limitation occurs when the airway is narrowed or blocked during breathing, resulting in obstructed airflow and a flattened inspiratory signal. Flow limitation is a common respiratory feature in patients with several respiratory diseases. For example, COPD is characterized by persistent airflow restriction, and patients with sleep apnea and hypoventilation syndrome also experience flow-limited breathing events due to airway obstruction during sleep. Flow-limited breathing events are one of the parameters monitored in sleep apnea screening devices and home CPAP machines, and the airflow limitation index is an important parameter for assessing respiratory disorders.

[0003] In existing technologies, airflow limitation is typically determined by calculating indicators such as amplitude, roundness, flatness, and kurtosis to detect changes in the trend of these indicators over multiple respiratory cycles. However, this method requires detecting parameter changes over several consecutive respiratory cycles, resulting in a relatively delayed assessment. Alternatively, airflow limitation can be determined by calculating the mean and variance characteristics of the first inspiratory segment of the respiratory signal, but this method is susceptible to noise interference and has low sensitivity. Summary of the Invention

[0004] In order to at least overcome the above-mentioned deficiencies in the prior art, the purpose of this application is to provide a detection device and a ventilator for respiratory restriction events.

[0005] In a first aspect, embodiments of this application provide a device for detecting respiratory restriction events, the device comprising: a first acquisition module, configured to acquire a respiratory curve of a user wearing the ventilator, wherein the horizontal axis of the respiratory curve is the detection time and the vertical axis is the respiratory airflow amplitude;

[0006] The second acquisition module is used to acquire the peak amplitude and the first inspiratory period of the inspiratory curve based on the inspiratory curve of the breathing curve.

[0007] The determination module is used to determine an amplitude threshold based on the peak amplitude and a pre-configured amplitude coefficient, and to determine a second inhalation period within the first inhalation period according to the amplitude threshold;

[0008] The detection module is used to construct similar triangles based on the first inspiratory period and the second inspiratory period, and to detect whether a user wearing the ventilator has experienced a respiratory restriction event based on the similarity area ratio of the constructed similar triangles.

[0009] In one possible implementation, the determining module is specifically used for:

[0010] A first amplitude threshold is determined based on the peak amplitude and a pre-configured first amplitude coefficient, and a first moment and a second moment are determined when the inhalation curve passes through the first amplitude threshold, wherein the first moment is less than the second moment.

[0011] The second inhalation period is determined based on the positions of the first time and the second time on the first inhalation period. When the first time is not greater than the maximum value of the first interval of the first inhalation period and the second time is not less than the minimum value of the first interval of the first inhalation period, the second inhalation period is determined based on the first time and the second time.

[0012] When the first time point is greater than the maximum value of the first interval of the first inhalation period, or when the second time point is less than the minimum value of the first interval of the first inhalation period, a new first time point and a second time point are determined, and a second inhalation period is determined based on the new first time point and the second time point.

[0013] In one possible implementation, the determining module is further configured to:

[0014] When the first moment is greater than the maximum value of the first interval of the first inhalation period, or when the second moment is less than the minimum value of the first interval of the first inhalation period, the midpoint moment of the first inhalation period is determined, and the amplitude of the midpoint moment is obtained.

[0015] A second amplitude threshold is determined based on the amplitude at the intermediate moment and a pre-configured second amplitude coefficient, and a new first moment and a new second moment are determined after the inhalation curve passes through the second amplitude threshold. A second inhalation period is then determined based on the new first moment and the new second moment.

[0016] In one possible implementation, the determining module is further configured to:

[0017] Based on the first amplitude threshold or the second amplitude threshold, draw a straight line parallel to the horizontal axis, and the straight line intersects the inhalation curve at two or more points.

[0018] When the straight line and the inhalation curve intersect at two points, the two intersection points are respectively taken as the first time point and the second time point;

[0019] When the straight line and the inhalation curve have more than two intersection points, the two intersection points with the greatest relative distance are respectively taken as the first time point and the second time point.

[0020] In one possible implementation, the detection module is specifically used for:

[0021] Based on the start and end times of the first inhalation period, and the first and second times of the second inhalation period, a first inhalation triangle and a second inhalation triangle with the same vertex are constructed, wherein the first inhalation triangle and the second inhalation triangle are similar triangles.

[0022] Based on the area ratio of the first inspiratory triangle and the second inspiratory triangle, it is determined whether a user wearing the ventilator has experienced a respiratory restriction event.

[0023] In one possible implementation, the detection module is specifically used for:

[0024] When the ratio of the similarity area of ​​the first inspiratory triangle and the second inspiratory triangle is greater than a preset value, the detection result is that the user wearing the ventilator has experienced a breathing restriction event.

[0025] When the ratio of the similarity area of ​​the first inspiratory triangle and the second inspiratory triangle is not greater than a preset value, the detection result is that the user wearing the ventilator has not experienced a breathing restriction event.

[0026] In one possible implementation, the first acquisition module is specifically used to: perform bandpass filtering on the respiratory airflow signal of the ventilator to acquire the respiratory airflow information of the user wearing the ventilator, and construct the respiratory curve based on the user's respiratory airflow information.

[0027] In one possible implementation, the device further includes a sending module and a display module;

[0028] The sending module is used to record the time and duration of the breathing restriction event when a breathing restriction event is detected in a user wearing the ventilator, and then send it to the display module.

[0029] The display module is used to display the status parameters of the ventilator.

[0030] Secondly, embodiments of this application also provide a ventilator, comprising:

[0031] Memory, used to store one or more programs;

[0032] The processor is used to perform the functions of the detection device for any of the breathing restriction events in the first aspect.

[0033] Secondly, embodiments of this application also provide a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, performs the function of a detection device for any of the breathing restriction events described in the first aspect.

[0034] Based on any of the above aspects, the respiratory restriction event detection device and ventilator provided in the embodiments of this application can acquire a first inspiratory period by a second acquisition module, determine a second inspiratory period by a determination module, and construct similar triangles based on the first and second inspiratory periods by a detection module. The morphological characteristics of the inspiratory curve are characterized by the ratio of the similar areas of the similar triangles. According to the theorem of similar triangles, the ratio of the similar areas is equal to the square of the similarity ratio of the similar triangles. Therefore, the morphological characteristics of the inspiratory curve can be characterized by the ratio of the first and second inspiratory periods. This device has the advantages of low computational load, strong anti-interference ability, and good real-time performance. Attached Figure Description

[0035] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings required in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of this application and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0036] Figure 1 A functional block diagram of the respiratory restriction event detection device provided in the embodiments of this application;

[0037] Figure 2 This is a schematic diagram of one possible similar triangle;

[0038] Figure 3 This is a schematic diagram of another possible similar triangle. Detailed Implementation

[0039] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. The components of the embodiments of this application described and shown in the accompanying drawings can generally be arranged and designed in various different configurations.

[0040] Therefore, the following detailed description of the embodiments of this application provided in the accompanying drawings is not intended to limit the scope of the claimed application, but merely to illustrate selected embodiments of the application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without inventive effort are within the scope of protection of this application.

[0041] It should be noted that similar labels and letters in the following figures indicate similar items. Therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures.

[0042] In the description of this application, it should be noted that the terms "upper," "lower," etc., indicating the orientation or positional relationship are based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship commonly used when the product is in use. They are used only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation on this application. In addition, the terms "first," "second," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0043] In the description of this application, it should also be noted that, unless otherwise expressly specified and limited, the terms "set up," "connected," "linked," and "connected" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0044] It should be noted that, where there is no conflict, different features in the embodiments of this application can be combined with each other.

[0045] Please refer to Figure 1 This application provides a detection device 100 for respiratory restriction events applied to a ventilator. The device includes a first acquisition module 110, a second acquisition module 120, a determination module 130, and a detection module 140.

[0046] The first acquisition module 110 is used to acquire the respiratory curve of a user wearing a ventilator. The horizontal axis of the respiratory curve is the detection time, and the vertical axis is the respiratory airflow amplitude. In the respiratory curve, the inspiratory curve (also called the inspiratory phase) can be considered as the part of the curve where the respiratory airflow amplitude is greater than zero, and the expiratory curve (also called the gas phase) can be considered as the part of the curve where the respiratory airflow amplitude is less than zero.

[0047] The second acquisition module 120 is used to acquire the peak amplitude of the inspiratory curve and the first inspiratory period based on the respiratory curve, wherein the first inspiratory period can be the inspiratory period within a respiratory cycle.

[0048] The determination module 130 is used to determine the amplitude threshold based on the peak amplitude and the pre-configured amplitude coefficient, and to determine the second inspiratory period within the first inspiratory period according to the amplitude threshold. Specifically, a straight line parallel to the horizontal axis can be drawn based on the first amplitude threshold, and the second inspiratory period can be determined based on the intersection of the straight line and the inspiratory curve within a certain respiratory cycle.

[0049] It should be noted that the amplitude coefficient can be obtained by building a neural network model and using the neural network model to extract the image features of the breathing waveform under respiratory restriction.

[0050] The detection module 140 is used to construct similar triangles based on the first inspiratory period and the second inspiratory period, and to detect whether a user wearing a ventilator has experienced a respiratory restriction event based on the similarity area ratio of the constructed similar triangles.

[0051] In this embodiment, the second acquisition module 120 can acquire the first inhalation period, the determination module 130 can determine the second inhalation period, and the detection module 140 can construct similar triangles based on the first and second inhalation periods. The morphological characteristics of the inhalation curve are characterized by the ratio of the similar areas of the similar triangles. According to the theorem of similar triangles, the ratio of the similar areas is equal to the square of the similarity ratio of the similar triangles. Therefore, the morphological characteristics of the inhalation curve can be characterized by the ratio of the first and second inhalation periods. This method has the advantages of low computational load, strong anti-interference ability, and good real-time performance.

[0052] As one possible implementation of this application, the determining module 130 can be used to implement the following functions.

[0053] A first amplitude threshold is determined based on the peak amplitude and a pre-configured first amplitude coefficient. The first and second moments when the inspiratory curve crosses the first amplitude threshold are then determined, with the first moment being less than the second moment. Specifically, a straight line parallel to the horizontal axis can be drawn based on the first amplitude threshold. This line typically intersects the inspiratory curve within a respiratory cycle at two or more points. When the line intersects the inspiratory curve at two points, the moments corresponding to these two intersections can be recorded as the first and second moments. When the line intersects the inspiratory curve at more than two points, the moments corresponding to the two intersections with the greatest relative distance can be recorded as the first and second moments, with the second moment being greater than the first moment. For example, the peak height can be denoted as H, the amplitude coefficient as Thr1, and the first amplitude threshold as h, where h = H * Thr1.

[0054] The second inhalation period is determined based on the positions of the first and second times within the first inhalation period. The second inhalation period is determined when the first time is not greater than the maximum value of the first interval of the first inhalation period, and the second time is not less than the minimum value of the first interval of the first inhalation period. For example, the first inhalation period can be denoted as W, the minimum value of the first interval can be 0.4*W, and the maximum value of the first interval can be 0.6*W. When the first time is not greater than 0.6*W and the second time is not less than 0.4*W, the time interval corresponding to the first and second times can be taken as the second inhalation period w1.

[0055] When the first time point is greater than the maximum value of the first interval of the first inhalation period, or when the second time point is less than the minimum value of the first interval of the first inhalation period, a new first time point and a new second time point are determined, and a second inhalation period is determined based on the new first time point and the new second time point.

[0056] Specifically, when the first moment is greater than the maximum value of the first interval of the first inspiratory period, or when the second moment is less than the minimum value of the first interval of the first inspiratory period, the midpoint of the first inspiratory period is determined, and the amplitude of the midpoint is obtained. Based on the amplitude of the midpoint and a pre-configured second amplitude coefficient, a second amplitude threshold is determined, and new first and second moments after the inspiratory curve passes the second amplitude threshold are determined. The second inspiratory period is then determined based on these new first and second moments. Similarly, it should be noted that the second amplitude coefficient can be obtained by building a neural network model and extracting image features of the respiratory waveform under respiratory limitation conditions using the neural network model. For example, when the first moment is greater than 0.6*W, or the second moment is less than 0.4*W, the midpoint of the inspiratory curve within a certain respiratory cycle can be determined, and the amplitude of the midpoint is denoted as H_m, the second amplitude coefficient as Thr2, and the second amplitude threshold as h_m, where h_m = H_m*Thr2.

[0057] In this embodiment, the determining module 130 can determine the second inspiratory period under different breathing curves, thereby determining one side of two similar triangles.

[0058] As one possible implementation of this application embodiment, the detection module 140 can be used to implement the following functions.

[0059] Based on the start and end times of the first inhalation period, and the first and second times of the second inhalation period, construct a first inhalation triangle and a second inhalation triangle with the same vertex. Specifically, the start and first times determine a straight line, and the end and second times determine another straight line. The intersection of the two straight lines determines the vertex of the triangle. Therefore, the first and second inhalation triangles are similar triangles. Please refer to [reference needed] for details. Figure 2 and Figure 3 , Figure 2 An example is shown where similar triangles are constructed when the first and second time points are within the first interval, where h1 is the height of the second inhalation triangle. Figure 3 Examples of similar triangles are constructed when the first and second time points are not located in the first interval, where h2 is the height of the second inhalation triangle.

[0060] Based on the area ratio of the first inspiratory triangle and the second inspiratory triangle, the system detects whether a user wearing a ventilator has experienced a respiratory restriction event. Specifically, when the similarity area ratio of the first and second inspiratory triangles is greater than a preset value, the detection result indicates that the user wearing a ventilator has experienced a respiratory restriction event; when the similarity area ratio of the first and second inspiratory triangles is not greater than the preset value, the detection result indicates that the user wearing a ventilator has not experienced a respiratory restriction event. For example, the preset value can be between 0.25 and 0.5.

[0061] In this embodiment, the detection module 140 can construct similar triangles based on the first inhalation period and the second inhalation period. The morphological characteristics of the inhalation curve are characterized by the ratio of the similar areas of the similar triangles. According to the theorem of similar triangles, the ratio of the similar areas is equal to the square of the similarity ratio of the similar triangles. Therefore, the morphological characteristics of the inhalation curve can be characterized by the ratio of the first inhalation period and the second inhalation period. This has the advantages of low computational load, strong anti-interference ability, and good real-time performance.

[0062] As one possible implementation of this application embodiment, the first acquisition module 110 can perform bandpass filtering on the respiratory airflow signal of the ventilator to acquire the respiratory airflow information of the user wearing the ventilator, and construct a respiratory curve based on the user's respiratory airflow information. For example, the first acquisition module 110 can perform bandpass filtering on the respiratory airflow signal of the ventilator from 0.03Hz to 5Hz.

[0063] Furthermore, the breathing restriction event detection device 100 provided in the request may also include a transmitting module and a display module. The transmitting module records the time and duration of the breathing restriction event when it is detected in a user wearing a ventilator, and sends this information to the display module. The display module displays the ventilator's status parameters. Through the transmitting and display modules, the user's breathing status can be quickly viewed.

[0064] Based on the same inventive concept, this application also provides a ventilator, which may include a memory and a processor, wherein the memory is used to store one or more programs, and the processor is used to execute the function of the detection device 100 for any of the breathing restriction events in the above embodiments.

[0065] This application also provides a computer-readable storage medium storing a computer program thereon, which, when executed by a processor, implements the function of the detection device 100 for any of the breathing restriction events described in the above embodiments.

[0066] In summary, this embodiment provides a detection device and ventilator for respiratory restriction events. The second acquisition module can acquire the first inspiratory period, the determination module can determine the second inspiratory period, and the detection module can construct similar triangles based on the first and second inspiratory periods. The morphological characteristics of the inspiratory curve are characterized by the ratio of the similar areas of the similar triangles. According to the theorem of similar triangles, the ratio of the similar areas is equal to the square of the similarity ratio of the similar triangles. Therefore, the morphological characteristics of the inspiratory curve can be characterized by the ratio of the first and second inspiratory periods. This method has the advantages of low computational load, strong anti-interference ability, and good real-time performance.

[0067] The above description is merely a preferred embodiment of this application and is not intended to limit this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. A device for detecting respiratory restriction events, characterized in that, For use in ventilators, the device includes: The first acquisition module is used to acquire the breathing curve of a user wearing the ventilator, wherein the horizontal axis of the breathing curve is the detection time and the vertical axis is the respiratory airflow amplitude. The second acquisition module is used to acquire the peak amplitude and the first inspiratory period of the inspiratory curve based on the inspiratory curve of the breathing curve. The determination module is used to determine an amplitude threshold based on the peak amplitude and a pre-configured amplitude coefficient, and to determine a second inhalation period within the first inhalation period according to the amplitude threshold; The detection module is used to construct similar triangles based on the first inspiratory period and the second inspiratory period, and to detect whether a user wearing the ventilator has experienced a respiratory restriction event based on the similarity area ratio of the constructed similar triangles.

2. The detection device for respiratory restriction events as described in claim 1, characterized in that, The determining module is specifically used for: A first amplitude threshold is determined based on the peak amplitude and a pre-configured first amplitude coefficient, and a first moment and a second moment are determined when the inhalation curve passes through the first amplitude threshold, wherein the first moment is less than the second moment. The second inhalation period is determined based on the positions of the first time and the second time on the first inhalation period. When the first time is not greater than the maximum value of the first interval of the first inhalation period and the second time is not less than the minimum value of the first interval of the first inhalation period, the second inhalation period is determined based on the first time and the second time. When the first time point is greater than the maximum value of the first interval of the first inhalation period, or when the second time point is less than the minimum value of the first interval of the first inhalation period, a new first time point and a second time point are determined, and a second inhalation period is determined based on the new first time point and the second time point.

3. The detection device for respiratory restriction events as described in claim 2, characterized in that, The determining module is further specifically used for: When the first moment is greater than the maximum value of the first interval of the first inhalation period, or when the second moment is less than the minimum value of the first interval of the first inhalation period, the midpoint moment of the first inhalation period is determined, and the amplitude of the midpoint moment is obtained. A second amplitude threshold is determined based on the amplitude at the intermediate moment and a pre-configured second amplitude coefficient, and a new first moment and a new second moment are determined after the inhalation curve passes through the second amplitude threshold. A second inhalation period is then determined based on the new first moment and the new second moment.

4. The detection device for respiratory restriction events as described in claim 3, characterized in that, The determining module is further specifically used for: Based on the first amplitude threshold or the second amplitude threshold, draw a straight line parallel to the horizontal axis, and the straight line intersects the inhalation curve at two or more points. When the straight line and the inhalation curve intersect at two points, the two intersection points are respectively taken as the first time point and the second time point; When the straight line and the inhalation curve have more than two intersection points, the two intersection points with the greatest relative distance are respectively taken as the first time point and the second time point.

5. The detection device for respiratory restriction events according to claim 1, characterized in that, The detection module is specifically used for: Based on the start and end times of the first inhalation period, and the first and second times of the second inhalation period, a first inhalation triangle and a second inhalation triangle with the same vertex are constructed, wherein the first inhalation triangle and the second inhalation triangle are similar triangles. Based on the area ratio of the first inspiratory triangle and the second inspiratory triangle, it is determined whether a user wearing the ventilator has experienced a respiratory restriction event.

6. The device for detecting respiratory restriction events according to claim 5, characterized in that, The detection module is specifically used for: When the ratio of the similarity area of ​​the first inspiratory triangle and the second inspiratory triangle is greater than a preset value, the detection result is that the user wearing the ventilator has experienced a breathing restriction event. When the ratio of the similarity area of ​​the first inspiratory triangle and the second inspiratory triangle is not greater than a preset value, the detection result is that the user wearing the ventilator has not experienced a breathing restriction event.

7. The device for detecting respiratory restriction events according to claim 1, characterized in that, The first acquisition module is specifically used for: The respiratory airflow signal of the ventilator is bandpass filtered to obtain the respiratory airflow information of the user wearing the ventilator, and the respiratory curve is constructed based on the user's respiratory airflow information.

8. The detection device for respiratory restriction events according to claim 1, characterized in that, The device also includes a transmitting module and a display module; The sending module is used to record the time and duration of the breathing restriction event when a breathing restriction event is detected in a user wearing the ventilator, and then send it to the display module. The display module is used to display the status parameters of the ventilator.

9. A ventilator, characterized in that, include: Memory, used to store one or more programs; A processor for performing the functions of the detection device for any one of claims 1-8 regarding a respiratory restriction event.

10. A computer-readable storage medium, characterized in that, It stores a computer program that, when executed by a processor, performs the function of the detection device for respiratory restriction events as described in any one of claims 1-8.

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