Respiratory impedance measuring system and respiratory impedance measuring method

Abstract

A respiratory impedance measurement system (100) and a respiratory impedance measurement method, the system comprising: an oscillation module (1) for generating an oscillatory wave airflow; the connection module (2) is connected with the oscillation module (1), and the connection module (2) is used for transmitting the oscillation wave airflow generated by the oscillation module (1) to a subject and receiving target breathing airflow exhaled by the subject; the detection module (3) is used for detecting the gas pressure and the gas flow of the target breathing airflow in the connection module (2) to obtain a gas pressure signal and a gas flow signal respectively; the calculation module (4) is connected with the detection module (3), and the calculation module (4) is used for calculating the impedance of the respiratory system of the subject according to the gas pressure signal and the gas flow signal; and according to the set result output mode, storing the impedance to a local memory space, and / or uploading the impedance to a medical data management platform.

Description

Respiratory impedance measurement system and respiratory impedance measurement method Technical Field

[0001] The present application relates to the technical field of impedance measurement of a human respiratory system, and in particular to a respiratory impedance measurement system and a respiratory impedance measurement method. Background Art

[0002] Currently, measuring a person's respiratory impedance is necessary to detect pathological changes in their lung function. However, existing devices, systems, and methods for measuring the impedance of the human respiratory system are often complex and limited in functionality, failing to meet the demands of today's big data era.

[0003] Summary of the Invention

[0004] In response to the problems of complex structures and difficulty in adapting to the development of the big data era in current human respiratory system impedance measurement equipment, systems and methods, the embodiments of the present application provide a respiratory impedance measurement system and a respiratory impedance measurement method.

[0005] The respiratory impedance measurement system provided in an embodiment of the present application is used to measure the impedance of the respiratory system of a subject, and includes an oscillation module, a connection module, a detection module and a calculation module, wherein the oscillation module is used to generate an oscillating wave airflow; the connection module is connected to the oscillation module, and is used to transmit the oscillating wave airflow generated by the oscillation module to the subject and receive the target respiratory airflow exhaled by the subject; the detection module is used to detect the gas pressure and gas flow of the target respiratory airflow in the connection module to obtain a gas pressure signal and a gas flow signal respectively; the calculation module is connected to the detection module, and is used to calculate the impedance of the respiratory system of the subject based on the gas pressure signal and the gas flow signal; the calculation module is also used to save the impedance to the local memory space according to the set result output mode, and / or upload the impedance to the medical data management platform.

[0006] The respiratory impedance measurement method provided in an embodiment of the present application is applied to a respiratory impedance measurement system, and the respiratory impedance measurement system includes an oscillation module. The method includes: generating an oscillating wave airflow through the oscillation module; transmitting the oscillating wave airflow generated by the oscillation module to a subject and receiving a target respiratory airflow exhaled by the subject; detecting the gas pressure and gas flow of the target respiratory airflow to obtain a gas pressure signal and a gas flow signal, respectively; calculating the impedance of the subject's respiratory system based on the gas pressure signal and the gas flow signal; and saving the impedance to a local memory space and / or uploading the impedance to a medical data management platform according to a set result output method.

[0007] The respiratory impedance measurement system and the respiratory impedance measurement method provided in the embodiments of the present application can not only accurately measure the impedance of the human respiratory system with a simple structure, but also save the impedance to the local memory space and / or upload the impedance to the medical data management platform, making the management of the retrieval and application of the impedance more convenient, which is conducive to adapting to the development of the big data era. BRIEF DESCRIPTION OF THE DRAWINGS

[0008] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following briefly introduces the drawings required for describing the embodiments.

[0009] FIG1 is a schematic diagram of the composition of a respiratory impedance measurement system provided in one embodiment of the present application;

[0010] FIG2 is a schematic diagram of the partial structure and composition of the respiratory impedance measurement system provided in one embodiment of the present application;

[0011] FIG3 is a schematic structural diagram of a vibrating element in an oscillation module of a respiratory impedance measurement system provided in one embodiment of the present application;

[0012] FIG4 is a schematic diagram of a respiratory impedance measurement system according to another embodiment of the present application;

[0013] FIG5 is a schematic diagram of the partial composition and structure of a respiratory impedance measurement system provided by another embodiment of the present application;

[0014] FIG6 is a schematic structural diagram of a respiratory impedance measurement system provided by another embodiment of the present application;

[0015] FIG7 is a flow chart of a respiratory impedance measurement method according to an embodiment of the present application;

[0016] FIG8 is a schematic diagram of a sub-flow diagram of step 704 in FIG7 according to an embodiment of the present application;

[0017] FIG9 is a flow chart of a respiratory impedance measurement method according to another embodiment of the present application. DETAILED DESCRIPTION

[0018] The technical solutions in the embodiments of the present application will be described clearly and completely below in conjunction with the drawings in the embodiments of the present application.

[0019] It will be understood that when used in this specification and the appended claims, the terms “comprises” and “comprising” indicate the presence of described features, integers, steps, operations, elements and / or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components and / or groups thereof.

[0020] It should also be understood that the terms used in this specification are for the purpose of describing specific embodiments only and are not intended to limit the present application. As used in this specification and the appended claims, the singular forms "a," "an," and "the" are intended to include the plural forms unless the context clearly indicates otherwise.

[0021] It should be further understood that the term "and / or" used in this specification and the appended claims refers to and includes any and all possible combinations of one or more of the associated listed items.

[0022] The terms "respiratory impedance," "impedance," and "impedance of the respiratory system" used herein are all understood to refer to the impedance of the human respiratory system, an important indicator in pulmonary function tests. It should be understood that the terms "impedance of the respiratory system," "respiratory impedance," "impedance," and "impedance of the human respiratory system" are synonymous and can be used interchangeably.

[0023] Please refer to FIG1 , which is a schematic diagram of the composition of a respiratory impedance measurement system provided in one embodiment of the present application.

[0024] The respiratory impedance measurement system 100 includes an oscillation module 1 , a connection module 2 , a detection module 3 and a calculation module 4 .

[0025] The aforementioned oscillation module 1 is used to generate oscillating wave airflow.

[0026] The connecting module 2 is connected to the oscillating module 1 . The connecting module 2 is used to transmit the oscillating wave airflow generated by the oscillating module 1 to the subject 5 and receive the target respiratory airflow exhaled by the subject 5 .

[0027] The detection module 3 is used to detect the gas pressure and gas flow of the target respiratory airflow in the connection module 2 to obtain a gas pressure signal and a gas flow signal respectively.

[0028] The aforementioned computing module 4 is connected to the aforementioned detection module 3, and the aforementioned computing module 4 is used to calculate the impedance of the respiratory system of the subject 5 based on the aforementioned gas pressure signal and the aforementioned gas flow signal; and is used to save the aforementioned impedance to the local memory space according to the set result output method, and / or upload the aforementioned impedance to the medical data management platform.

[0029] The embodiment of the present application generates the aforementioned oscillatory wave airflow and applies it to the spontaneous breathing airflow of the subject 5, which can generate a corresponding oscillatory wave airflow in the respiratory system of the subject 5, thereby strengthening the intensity of the airflow inhaled by the subject 5. The value related to the aforementioned respiratory impedance in the respiratory airflow exhaled by the subject 5 after being subjected to the oscillatory wave airflow will also be amplified, so that the gas pressure signal and gas flow signal obtained by respectively detecting the gas pressure and gas flow of the current airflow will also be stronger, and the detection module 3 is arranged in the aforementioned connection module 2, which can directly detect the gas pressure and gas flow of the current airflow. Therefore, the aforementioned respiratory impedance measurement system 100 provided by the embodiment of the present application can effectively detect the impedance of the respiratory system of the subject 5 with a simple structure, and after measuring the aforementioned impedance, it also saves the aforementioned impedance to the local memory space, and at the same time and / or uploads the aforementioned impedance to the aforementioned medical data management platform for reference and diagnosis by medical personnel. Therefore, not only can the aforementioned impedance be saved to the local memory space, but the aforementioned respiratory impedance measurement system 100 can also interact with the aforementioned medical data management platform, making the management of the aforementioned impedance such as retrieval and application more convenient, which is conducive to adapting to the development of the big data era.

[0030] Among them, the aforementioned medical data management platform can be a platform located on the server side for aggregating and managing medical data. Medical personnel can manage the aforementioned medical data uploaded by the aforementioned respiratory impedance measurement system 100 or other medical detection equipment located in various places through the aforementioned medical data management platform, and diagnose patients based on the corresponding medical data, wherein the aforementioned medical data includes the aforementioned impedance.

[0031] The oscillating wave airflow may be of a single frequency or a composite frequency. When the oscillating wave airflow is of a single frequency, the oscillating wave airflow is a sinusoidal wave airflow. When the oscillating wave airflow is of a composite frequency, the oscillating wave airflow is a pulse wave airflow. Regardless of whether the oscillating wave airflow is of a single frequency or a composite frequency, the frequency range of the oscillating wave airflow is 3 to 50 Hz.

[0032] The aforementioned gas pressure signal is a detected curve showing the change of the gas pressure of the aforementioned target respiratory airflow with respect to time, and the aforementioned gas flow signal is a detected curve showing the change of the gas flow of the aforementioned target respiratory airflow with respect to time.

[0033] The aforementioned output method includes simultaneously saving the aforementioned impedance to local memory and uploading the aforementioned impedance to a medical data management platform, saving the aforementioned impedance only to local memory, and uploading the aforementioned impedance only to a medical data management platform. The aforementioned output method can be a pre-set default setting or a user-selectable setting.

[0034] In some embodiments, one end of the aforementioned connecting module 2 is connected to the aforementioned oscillation module 1, and the other end is used to be inserted into the mouth of the subject 5 when measuring the impedance of the respiratory system of the subject 5. The aforementioned connecting module 2 is used to transmit the aforementioned oscillation wave airflow generated by the aforementioned oscillation module 1 to the subject 5 when measuring the impedance of the respiratory system of the subject 5, and is used to receive the aforementioned target respiratory airflow exhaled by the subject 5 after the aforementioned oscillation wave airflow is applied.

[0035] In some embodiments, the aforementioned detection module 3 is disposed within the aforementioned connection module 2, thereby being able to directly detect the gas pressure and gas flow of the target respiratory airflow transmitted within the aforementioned connection module 2 and obtain the aforementioned gas pressure signal and the aforementioned gas flow signal, respectively. In other embodiments, the aforementioned detection module 3 may also be disposed outside the aforementioned connection module 2, for example, at the connection between the aforementioned detection module 3 and the aforementioned calculation module 4 or the aforementioned oscillation module 1, thereby also being able to detect the gas pressure and gas flow of the aforementioned target respiratory airflow and obtain the aforementioned gas pressure signal and the aforementioned gas flow signal, respectively. The aforementioned detection module 3 samples and detects the gas pressure and gas flow of the aforementioned target respiratory airflow through a sampling tube connected to the aforementioned connection module 2 and obtains the aforementioned gas pressure signal and the aforementioned gas flow signal, respectively.

[0036] In some embodiments, the aforementioned computing module 4 calculates the impedance of the respiratory system of the subject 5 based on the aforementioned gas pressure signal and the aforementioned gas flow signal, including: the aforementioned computing module 4 performs denoising processing on the aforementioned gas pressure signal and the aforementioned gas flow signal, respectively; the aforementioned computing module 4 calculates the quotient of the Fourier transform of the aforementioned gas pressure signal and the aforementioned gas flow signal after denoising processing to obtain the impedance of the respiratory system of the subject 5, wherein the aforementioned impedance includes respiratory resistance and respiratory reactance.

[0037] In some embodiments, the respiratory impedance measurement system 100 may include a memory (not shown), and the calculation module 4 saving the impedance to a local memory space may refer to storing the impedance in the memory.

[0038] Please refer to FIG. 2 , which is a schematic diagram showing a partial structure and components of the respiratory impedance measurement system 100 provided in one embodiment of the present application.

[0039] The aforementioned oscillation module 1 includes a waveform generator 11 and a vibration element 12. The aforementioned vibration element 12 is connected between the aforementioned connection module 2 and the aforementioned waveform generator 11. The aforementioned waveform generator 11 is used to generate an oscillation excitation signal of a single frequency or a composite frequency. The aforementioned vibration element 12 is used to generate the aforementioned oscillation wave airflow under the drive of the aforementioned oscillation excitation signal.

[0040] Furthermore, the oscillating wave airflow generated by the vibration element 12 is transmitted to the subject 5 through the connection module 2 .

[0041] Please refer to Figure 3, which is a structural schematic diagram of the aforementioned vibration element 12 in the aforementioned oscillation module of the aforementioned respiratory impedance measurement system 100 provided in one embodiment of the present application, wherein (A) in Figure 3 is a left view of the aforementioned vibration element 12, (B) in Figure 3 is a front view of the aforementioned vibration element 12, (C) in Figure 3 is a bottom view of the aforementioned vibration element 12, and (D) in Figure 3 is a three-dimensional stereoscopic image of the aforementioned vibration element 12.

[0042] The vibration element 12 includes at least one speaker 121 and a box 122 .

[0043] The box body 122 has an outer surface and a cavity enclosed by the outer surface. The outer surface of the box body 122 is provided with an airflow outlet.

[0044] The at least one speaker 121 is arranged through the outer surface of the box 122, and the sound outlet of the at least one speaker 121 is arranged in the cavity of the box 122; the at least one speaker 121 is connected to the waveform generator 11 to receive the oscillation excitation signal generated by the waveform generator 11 to generate the oscillation wave airflow.

[0045] The gas outlet is connected to the connection module 2. Thus, the sound-producing airflow generated by the at least one speaker 121 converges in the cavity to ultimately generate the oscillating wave airflow, which is then output to the connection module 2 through the airflow outlet.

[0046] In some embodiments, the airflow outlet is disposed on a side of the outer surface of the box 122 away from the at least one speaker 121 .

[0047] In other embodiments, the box body 122 is a polyhedron, and the number of faces of the box body 122 is greater than the number of the at least one speaker 121; each speaker 121 is respectively arranged in a different face of the box body 122, and the airflow outlet is arranged on a face of the outer surface of the box body 122 where the speaker 121 is not arranged.

[0048] Among them, (B) in Figure 3 is a front view with the side of the aforementioned box 122 where the aforementioned speaker 121 is not installed as the front, (A) in Figure 3 is a left view with the side of the aforementioned box 122 where the aforementioned speaker 121 is not installed as the front, and (C) in Figure 3 is an upward view with the side of the aforementioned box 122 where the aforementioned speaker 121 is not installed as the front.

[0049] The aforementioned sound-raising airflow is also an oscillating wave airflow of a single frequency or a composite frequency. This embodiment provides a vibration element 12. By setting a box body 122, the aforementioned vibration element 12 can integrate multiple small-sized speakers 121 into one, so that the diaphragms in multiple speakers 121 vibrate simultaneously to generate a larger sound-raising airflow, and finally converge into the aforementioned oscillating wave airflow with a stronger force in the aforementioned box body 122, which is not only beneficial to reducing the size of the equipment, but also beneficial to improving the detection quality.

[0050] The sound-producing airflow generated by each speaker 121 is identical, and the frequency of the sound-producing airflow is consistent with the frequency of the oscillating wave airflow. The greater the number of speakers 121 connected to the waveform generator 11, the stronger the intensity of the oscillating wave airflow formed by the sound-producing airflows converging in the box 122.

[0051] Please continue to refer to Figure 2. In other embodiments, the vibration element 12 includes a turbine and a drive motor. The turbine is installed in the connection module 2. The drive motor is connected between the turbine and the waveform generator 11. The drive motor is used to receive the oscillation excitation signal generated by the waveform generator 11 and drive the turbine to rotate to generate the oscillating wave airflow. In particular, the turbine generates the oscillating wave airflow having a certain frequency under the drive of the oscillation excitation signal, and the oscillating wave airflow generated by the turbine is determined by the oscillation excitation signal. The oscillating wave airflow generated by the turbine flows in the connection module 2 and is transmitted to the subject 5 through the connection module 2.

[0052] 2 , in some further embodiments, the vibration element 12 includes a gas storage assembly and a gas valve connected to a gas outlet in the gas storage assembly, and the gas valve is alternately opened and closed in response to the oscillation excitation signal.

[0053] Specifically, compressed air is stored in the aforementioned gas storage component, and the aforementioned gas storage component includes a compressed gas output port, which is sealed and connected to the aforementioned connecting module 2. The aforementioned gas valve is arranged at the aforementioned compressed gas output port and is connected to the aforementioned waveform generator 11, and is used to receive the aforementioned oscillation excitation signal generated by the aforementioned waveform generator 11. The aforementioned gas valve opens and closes alternately in response to the aforementioned oscillation excitation signal, thereby driving the aforementioned compressed air in the aforementioned gas storage component to intermittently enter the aforementioned connecting module 2 through the opened aforementioned gas valve, thereby generating the aforementioned oscillating wave airflow.

[0054] Please continue to refer to Figure 2. The aforementioned connection module 2 includes a measurement interface 21 and a gas pipe 22. The first end a of the aforementioned gas pipe 22 is connected to the vibration element 12 in the aforementioned oscillation module 1, and the second end b is connected to the aforementioned measurement interface 21. The aforementioned measurement interface 21 is used to extend into the oral cavity of the subject 5 when measuring the impedance of the respiratory system of the subject 5; the aforementioned gas pipe 22 is used to transmit the aforementioned oscillation wave airflow generated by the aforementioned oscillation module 1 to the subject 5 and to receive the aforementioned target respiratory airflow when measuring the impedance of the respiratory system of the subject 5. The aforementioned gas pipe 22 receiving the aforementioned target respiratory airflow means that the aforementioned target respiratory airflow exhaled by the subject 5 after the aforementioned oscillation wave airflow is applied finally flows outward through the aforementioned gas pipe 22. The aforementioned gas pipe 22 is a hollow pipe.

[0055] In some embodiments, as described above, the vibration element 12 includes the at least one speaker 121 and the housing 122. The airflow outlet on the outer surface of the housing 122 is connected to the first end a of the gas pipe 22. Thus, the sound-producing airflow generated by the at least one speaker 121 converges within the cavity, ultimately generating the oscillating wave airflow, which is then output through the airflow outlet to the gas pipe 22.

[0056] As described above and shown in FIG2 , in some embodiments, the aforementioned detection module 3 is disposed in the aforementioned gas pipe 22 , so that when the target respiratory airflow exhaled by the subject 5 after the aforementioned oscillating wave airflow is applied flows through the aforementioned gas pipe 22 , the aforementioned detection module 3 can detect the gas pressure and gas flow of the aforementioned target respiratory airflow and obtain a gas pressure signal and a gas flow signal, respectively.

[0057] The connection module 2 further includes a high-frequency blocking component, one end of which is connected to the gas pipe 22 and the other end is connected to the outside air, for realizing gas circulation inside and outside the gas pipe 22 and blocking the outflow of the oscillating wave airflow.

[0058] In some embodiments, the high-frequency blocking component includes a pipe branch 23 and a screen (not shown in the figure). The pipe branch 23 is connected to the gas pipe 22. The pipe branch 23 is used to allow external air to flow into the gas pipe 22 when measuring the impedance of the respiratory system of the subject 5, so as to provide breathing for the subject 5; the screen (not shown in the figure) is arranged at the connection c between the pipe branch 23 and the gas pipe 22. The aperture of each mesh in the screen (not shown in the figure) is relatively small, for example, it can be at the micron to millimeter level. Due to the diffraction effect of the oscillation wave, the oscillation wave airflow in the gas pipe 22 cannot pass through the screen (not shown in the figure) and flow from the pipe branch 23 to the air, but it does not affect the low-frequency airflow through the screen (not shown in the figure) into the gas pipe 22 for breathing by the subject 5. Therefore, the function of the aforementioned high-frequency barrier component not only includes allowing external air to flow into the aforementioned gas pipe 22 for the subject 5 to breathe, but also prevents the aforementioned oscillating wave airflow from flowing out into the air, that is, the aforementioned high-frequency barrier component can realize the gas circulation inside and outside the aforementioned gas pipe 22 and block the aforementioned oscillating wave airflow from flowing out.

[0059] In other embodiments, the high-frequency blocking assembly includes a slender, curved tube that communicates with the gas tube 22. The slender, curved tube has a relatively small diameter, for example, on the order of millimeters. Consequently, due to the diffraction of the oscillating wave, the oscillating wave airflow in the gas tube 22 cannot pass through the slender, curved tube and flow out of the branch tube 23 into the air. However, this does not prevent low-frequency airflow from passing through the slender, curved tube and entering the gas tube 22 for breathing by the subject 5. Therefore, the slender, curved tube in the high-frequency blocking assembly enables air flow in and out of the gas tube 22, preventing the oscillating wave airflow from escaping.

[0060] In some embodiments, the aforementioned connection module 2 also includes a filter screen 24, which is installed in the aforementioned gas pipeline 22 near the aforementioned second end b, that is, near the aforementioned measurement interface 21. The aforementioned filter screen 24 is used to isolate pollutants and prevent the subject 5 from cross-infection during use.

[0061] In some embodiments, the aforementioned measurement interface 21 is a mouthpiece.

[0062] Please refer to Figures 4 and 5 together. Figure 4 is a schematic diagram of the composition of the respiratory impedance measurement system 100 provided in another embodiment of the present application, and Figure 5 is a schematic diagram of the structure of the support module of the respiratory impedance measurement system 100 provided in another embodiment of the present application.

[0063] In addition to the aforementioned oscillation module 1, the aforementioned connection module 2, the aforementioned detection module 3 and the aforementioned calculation module 4 (see Figure 1), the aforementioned respiratory impedance measurement system 100 also includes a support module 6. The aforementioned support module 6 is connected to the aforementioned connection module 2 and is used to support the cheek of the subject 5 when measuring the impedance of the respiratory system of the subject 5.

[0064] As shown in Figure 5, the aforementioned support module 6 includes a V-shaped support member and a driving mechanism. The aforementioned measurement interface 21 is arranged through the tip of the aforementioned V-shaped support member. The aforementioned driving mechanism is connected to the aforementioned V-shaped support member to adjust the angle of the aforementioned V-shaped support member to match the cheek of the subject 5, thereby supporting the cheek of the subject 5 when measuring the impedance of the respiratory system of the subject 5.

[0065] Please continue to refer to Figure 2 or Figure 5. In some embodiments, the aforementioned detection module 3 includes a pressure sensor and a flow sensor, wherein the aforementioned pressure sensor and the aforementioned flow sensor are respectively arranged at d and e of the aforementioned gas pipeline 22, and are both connected to the aforementioned calculation module 4. The aforementioned pressure sensor is used to detect the gas pressure in the aforementioned connection module 2 to obtain the aforementioned gas pressure signal, and the aforementioned flow sensor is used to detect the gas flow in the aforementioned connection module 2 to obtain the aforementioned gas flow signal.

[0066] It should be understood that the aforementioned pressure sensor and the aforementioned flow sensor should be arranged as close to the aforementioned measurement interface 21 as possible in the aforementioned gas pipeline 22, and the aforementioned pressure sensor should be arranged in the aforementioned gas pipeline 22 at a position closer to the aforementioned measurement interface 21 than the aforementioned flow sensor, so as to accurately detect the gas pressure and gas flow of the aforementioned target respiratory airflow.

[0067] In some embodiments, the aforementioned flow sensor is a differential pressure flow meter.

[0068] As described above, in some embodiments, the aforementioned computing module 4 calculates the impedance of the respiratory system of the subject 5 based on the aforementioned gas pressure signal and the aforementioned gas flow signal, including: the aforementioned computing module 4 performs denoising processing on the aforementioned gas pressure signal and the aforementioned gas flow signal, respectively; the aforementioned computing module 4 calculates the quotient of the Fourier transform of the aforementioned gas pressure signal and the aforementioned gas flow signal after denoising, and obtains the impedance of the respiratory system of the subject 5, wherein the aforementioned impedance includes respiratory resistance and respiratory reactance.

[0069] The denoising process includes removing low-frequency spontaneous breathing signals from the gas pressure signal and the gas flow signal as noise, and extracting the gas pressure signal and the gas flow signal caused by the oscillating wave airflow.

[0070] The calculation formula for the aforementioned "calculating the quotient of the Fourier transform of the aforementioned gas pressure signal and the aforementioned gas flow signal after denoising to obtain the impedance of the respiratory system of subject 5" is: Z(f)=P(f) / F(f)=R(f)+jX(f), wherein Z(f) represents the aforementioned impedance, P(f) represents the Fourier transform function of the aforementioned gas pressure signal after denoising, F(f) represents the Fourier transform function of the aforementioned gas flow signal after denoising, R(f) represents the aforementioned respiratory resistance, which is used to reflect the magnitude of the central airway resistance, and X(f) represents the aforementioned respiratory reactance, which is used to reflect the compliance of the peripheral lung tissue and thorax.

[0071] Please refer to FIG. 6 , which is a schematic structural diagram of the respiratory impedance measurement system 100 provided in another embodiment of the present application.

[0072] In some embodiments, as shown in Figure 6, the respiratory impedance measurement system 100 also includes a display module 7, which is connected to the calculation module 4. The display module 7 is used to display the frequency impedance curve of the subject 5 based on the impedance calculated by the calculation module 4, wherein the frequency impedance curve includes a frequency resistance curve and a frequency reactance curve, the frequency resistance curve is obtained based on the respiratory resistance, and the frequency reactance curve is obtained based on the respiratory reactance.

[0073] An embodiment of the present application further provides a respiratory impedance measurement method. Please refer to FIG7 , which is a flow chart of the aforementioned respiratory impedance measurement method provided in an embodiment of the present application.

[0074] The respiratory impedance measurement method is applied to a respiratory impedance measurement system, wherein the respiratory impedance measurement system includes an oscillation module. The method includes:

[0075] 701. Generate an oscillating wave airflow through the aforementioned oscillation module.

[0076] 702. Transmit the oscillating wave airflow generated by the oscillation module to the subject and receive the target respiratory airflow exhaled by the subject.

[0077] 703. Detect the gas pressure and gas flow of the target respiratory airflow to obtain a gas pressure signal and a gas flow signal, respectively.

[0078] 704. Calculate the impedance of the subject's respiratory system based on the aforementioned gas pressure signal and the aforementioned gas flow signal.

[0079] 705. According to the set result output mode, the impedance is saved to the local memory space and / or the impedance is uploaded to the medical data management platform.

[0080] The embodiment of the present application generates the aforementioned oscillating wave airflow and applies it to the subject's spontaneous breathing airflow, which can generate a corresponding oscillating wave airflow in the subject's respiratory system, thereby strengthening the intensity of the subject's inhaled airflow. The value related to the respiratory impedance in the respiratory airflow exhaled by the subject after being subjected to the oscillating wave airflow will also be amplified, so that the gas pressure signal and gas flow signal obtained by respectively detecting the gas pressure and gas flow of the current airflow will also be stronger. Therefore, the aforementioned respiratory impedance measurement method provided by the embodiment of the present application can effectively detect the impedance of the subject's respiratory system with a simple structure, and after measuring the aforementioned impedance, it will also save the aforementioned impedance to the local memory space, and / or upload the aforementioned impedance to the aforementioned medical data management platform for reference and diagnosis by medical personnel. Therefore, not only can the aforementioned impedance be saved to the local memory space, but the aforementioned respiratory impedance measurement system can also interact with the aforementioned medical data management platform, making the management of the retrieval and application of the aforementioned impedance more convenient, which is conducive to adapting to the development of the big data era.

[0081] Among them, the aforementioned medical data management platform can be a platform located on the server side for aggregating and managing medical data. Medical personnel can manage the aforementioned medical data uploaded by the aforementioned respiratory impedance measurement system or other medical detection equipment located in various places through the aforementioned medical data management platform, and diagnose patients based on the corresponding medical data, wherein the aforementioned medical data includes the aforementioned impedance.

[0082] The oscillating wave airflow may be of a single frequency or a composite frequency. When the oscillating wave airflow is of a single frequency, the oscillating wave airflow is a sinusoidal wave airflow. When the oscillating wave airflow is of a composite frequency, the oscillating wave airflow is a pulse wave airflow. Regardless of whether the oscillating wave airflow is of a single frequency or a composite frequency, the frequency range of the oscillating wave airflow is 3 to 50 Hz.

[0083] The aforementioned gas pressure signal is a detected curve showing the change of the gas pressure of the aforementioned target respiratory airflow with respect to time, and the aforementioned gas flow signal is a detected curve showing the change of the gas flow of the aforementioned target respiratory airflow with respect to time.

[0084] The aforementioned output method includes simultaneously saving the aforementioned impedance to local memory and uploading the aforementioned impedance to a medical data management platform, saving the aforementioned impedance only to local memory, and uploading the aforementioned impedance only to a medical data management platform. The aforementioned output method can be a pre-set default setting or a user-selectable setting.

[0085] In some embodiments, the aforementioned oscillation module includes a waveform generator 11 and a vibration element 12, and the aforementioned "generating an oscillating wave airflow through the aforementioned oscillation module" includes: the aforementioned waveform generator 11 generates an oscillation excitation signal of a single frequency or a composite frequency, and the aforementioned oscillation excitation signal drives the aforementioned vibration element 12 to generate the aforementioned oscillating wave airflow.

[0086] Furthermore, in some embodiments, as shown in Figure 4, the vibration element 12 includes a box body 122 and at least one speaker 121; the box body 122 has an outer surface and a cavity formed by the outer surface, and the outer surface of the box body 122 is provided with an air flow output port; the at least one speaker 121 is arranged through the outer surface of the box body 122, and the sound outlet of the at least one speaker 121 is arranged in the cavity of the box body 122; the at least one speaker 121 is connected to the waveform generator 11.

[0087] The oscillation excitation signal drives the vibration element 12 to generate the oscillation wave airflow, which includes: the at least one speaker 121 receives the oscillation excitation signal generated by the waveform generator 11 to generate the oscillation wave airflow.

[0088] Among them, (B) in Figure 3 is a front view with the side of the aforementioned box 122 where the aforementioned speaker 121 is not installed as the front, (A) in Figure 3 is a left view with the side of the aforementioned box 122 where the aforementioned speaker 121 is not installed as the front, and (C) in Figure 3 is an upward view with the side of the aforementioned box 122 where the aforementioned speaker 121 is not installed as the front.

[0089] The aforementioned sound-raising airflow is also an oscillating wave airflow of a single frequency or a composite frequency. This embodiment provides a vibration element 12. By setting a box body 122, the aforementioned vibration element 12 can integrate multiple small-sized speakers 121 into one, so that the diaphragms in multiple speakers 121 vibrate simultaneously to generate a larger sound-raising airflow, and finally converge into the aforementioned oscillating wave airflow with a stronger sound wave in the aforementioned box body 122, which is not only beneficial to reducing the size of the equipment, but also beneficial to improving the detection quality.

[0090] The sound-producing airflow generated by each speaker 121 is identical, and the frequency of the sound-producing airflow is consistent with the frequency of the oscillating wave airflow. The greater the number of speakers 121 connected to the waveform generator 11, the stronger the intensity of the oscillating wave airflow formed by the sound-producing airflows converging in the box 122.

[0091] Please refer to FIG8 , which is a schematic diagram of a sub-flow diagram of step 704 in FIG7 according to an embodiment of the present application.

[0092] 801. Perform denoising processing on the aforementioned gas pressure signal and the aforementioned gas flow signal.

[0093] 802. Calculate the quotient of the Fourier transform of the denoised gas pressure signal and the gas flow signal to obtain the impedance of the subject's respiratory system, wherein the impedance includes respiratory resistance and respiratory reactance.

[0094] The denoising process includes removing low-frequency spontaneous breathing signals from the gas pressure signal and the gas flow signal as noise, and extracting the gas pressure signal and the gas flow signal caused by the oscillating wave airflow.

[0095] The calculation formula for the aforementioned "calculating the quotient of the Fourier transform of the aforementioned gas pressure signal and the aforementioned gas flow signal after denoising to obtain the impedance of the subject's respiratory system" is: Z(f)=P(f) / F(f)=R(f)+jX(f), wherein Z(f) represents the aforementioned impedance, P(f) represents the Fourier transform function of the aforementioned gas pressure signal after denoising, F(f) represents the Fourier transform function of the aforementioned gas flow signal after denoising, R(f) represents the aforementioned respiratory resistance, which is used to reflect the magnitude of the central airway resistance, and X(f) represents the aforementioned respiratory reactance, which is used to reflect the compliance of the peripheral lung tissue and thorax.

[0096] Please refer to FIG. 9 , which is a flow chart of the respiratory impedance measurement method according to another embodiment of the present application.

[0097] 901. Generate oscillating wave airflow through the aforementioned oscillation module.

[0098] 902. Transmit the oscillating wave airflow generated by the oscillation module to the subject and receive the target respiratory airflow exhaled by the subject.

[0099] 903. Detect the gas pressure and gas flow of the target respiratory airflow to obtain a gas pressure signal and a gas flow signal, respectively.

[0100] 904. Calculate the impedance of the subject's respiratory system based on the aforementioned gas pressure signal and the aforementioned gas flow signal.

[0101] 905. According to the set result output mode, the impedance is saved to the local memory space and / or the impedance is uploaded to the medical data management platform.

[0102] 906. Display the frequency impedance curve of the subject.

[0103] Among them, steps 901-905 correspond to steps 701-705 respectively, and the relevant descriptions can refer to each other.

[0104] The aforementioned frequency impedance curve includes a frequency resistance curve and a frequency reactance curve. The aforementioned frequency resistance curve is obtained based on the aforementioned respiratory resistance, and the aforementioned frequency reactance curve is obtained based on the aforementioned respiratory reactance.

[0105] Among them, the method steps shown in Figures 7 to 9 of the present application correspond to the functions of the aforementioned system. For more specific details, please refer to the relevant description of the aforementioned system.

[0106] The above description is merely a specific embodiment of the present application, but the scope of protection of the present application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in the present application, and such modifications or substitutions should be included in the scope of protection of the present application. Therefore, the scope of protection of the present application should be based on the scope of protection of the claims.

Claims

1. A respiratory impedance measurement system for measuring the impedance of a subject's respiratory system, characterized in that: The respiratory impedance measurement system comprises: An oscillation module for generating an oscillating wave airflow; a connecting module connected to the oscillation module, the connecting module being used to transmit the oscillation wave airflow generated by the oscillation module to the subject and to receive the target respiratory airflow exhaled by the subject; a detection module, configured to detect the gas pressure and gas flow of the target respiratory airflow in the connection module to obtain a gas pressure signal and a gas flow signal, respectively; and A computing module is connected to the detection module, and is used to calculate the impedance of the subject's respiratory system based on the gas pressure signal and the gas flow signal; and is used to save the impedance to a local memory space and / or upload the impedance to a medical data management platform according to a set result output method.

2. The respiratory impedance measurement system according to claim 1, wherein The oscillation module includes a waveform generator and a vibration element. The vibration element is connected between the connection module and the waveform generator. The waveform generator is used to generate an oscillation excitation signal of a single frequency or a composite frequency. The vibration element is used to generate the oscillation wave airflow under the drive of the oscillation excitation signal.

3. The respiratory impedance measurement system according to claim 2, wherein: The vibration element includes a box and at least one speaker; The box body has an outer surface and a cavity enclosed by the outer surface, and an air flow outlet is provided on the outer surface of the box body; The at least one speaker is arranged on the outer surface of the box, and the sound outlet of the at least one speaker is arranged in the cavity of the box; the at least one speaker is connected to the waveform generator to receive the oscillation excitation signal generated by the waveform generator to generate the oscillating wave airflow.

4. The respiratory impedance measurement system according to claim 3, wherein: The airflow outlet is arranged on a side of the outer surface of the box body away from the at least one speaker.

5. The respiratory impedance measurement system according to claim 3, wherein: The box is a polyhedron, and the number of faces of the box is greater than the number of the at least one speaker; each speaker is respectively arranged in a different face of the box, and the airflow outlet is arranged on a face of the outer surface of the box where the speaker is not arranged.

6. The respiratory impedance measurement system according to claim 2, wherein: The vibration element includes a turbine and a drive motor. The turbine is installed at the first end of the gas pipeline. The drive motor is connected between the turbine and the waveform generator. The drive motor is used to receive the oscillation excitation signal generated by the waveform generator and drive the turbine to rotate to generate the oscillating wave airflow.

7. The respiratory impedance measurement system according to claim 2, wherein: The vibration element includes a gas storage component and a gas valve connected to a gas outlet in the gas storage component, and the gas valve is alternately opened and closed in response to the oscillation excitation signal.

8. The respiratory impedance measurement system according to claim 2, wherein: The connecting module includes a measuring interface and a gas pipeline. The first end of the gas pipeline is connected to the vibration element in the oscillation module, and the second end is connected to the measuring interface.

9. The respiratory impedance measurement system according to claim 8, characterized in that The connection module also includes a high-frequency blocking component, one end of which is connected to the gas pipeline and the other end is connected to the outside air, so as to realize gas circulation inside and outside the gas pipeline and block the outflow of the oscillating wave airflow.

10. The respiratory impedance measurement system according to claim 8, wherein: The respiratory impedance measurement system further includes a support module, which is connected to the connection module and is used to support the cheeks of the subject when measuring the impedance of the subject's respiratory system.

11. The respiratory impedance measurement system according to claim 10, wherein: The support module includes a V-shaped support member and a driving mechanism, wherein the measurement interface is arranged through the tip of the V-shaped support member, and the driving mechanism is connected to the V-shaped support member to adjust the angle of the V-shaped support member to fit the cheek of the subject.

12. The respiratory impedance measurement system according to claim 8, wherein The detection module includes a pressure sensor and a flow sensor, wherein the pressure sensor and the flow sensor are both arranged in the gas pipeline and connected to the calculation module. The pressure sensor is used to detect the gas pressure in the connection module to obtain the gas pressure signal, and the flow sensor is used to detect the gas flow in the connection module to obtain the gas flow signal.

13. The respiratory impedance measurement system according to claim 1, wherein: The calculation module calculates the impedance of the respiratory system of the subject according to the gas pressure signal and the gas flow signal, including: The computing module performs denoising processing on the gas pressure signal and the gas flow signal respectively; The calculation module calculates the quotient of the Fourier transform of the gas pressure signal and the gas flow signal after the denoising process to obtain the impedance of the subject's respiratory system, wherein the impedance includes respiratory resistance and respiratory reactance.

14. A respiratory impedance measurement method, applied to a respiratory impedance measurement system, characterized in that: The respiratory impedance measurement system includes an oscillation module, and the method includes: generating an oscillating wave airflow through the oscillation module; transmitting the oscillating wave airflow generated by the oscillation module to the subject and receiving the target respiratory airflow exhaled by the subject; detecting a gas pressure and a gas flow of the target respiratory airflow to obtain a gas pressure signal and a gas flow signal, respectively; calculating an impedance of the subject's respiratory system based on the gas pressure signal and the gas flow signal; and According to the set result output mode, the impedance is saved to the local memory space and / or the impedance is uploaded to the medical data management platform.

15. The respiratory impedance measurement method according to claim 14, characterized in that: The oscillation module includes a waveform generator and a vibration element, and the “generating an oscillating wave airflow by the oscillation module” includes: The waveform generator generates an oscillation excitation signal of a single frequency or a composite frequency, and the oscillation excitation signal drives the vibration element to generate the oscillation wave airflow.

16. The respiratory impedance measurement method according to claim 15, characterized in that: The vibration element includes a box and at least one speaker; the box has an outer surface and a cavity enclosed by the outer surface, and the outer surface of the box is provided with an airflow outlet; the at least one speaker is provided through the outer surface of the box, and the sound outlet of the at least one speaker is provided in the cavity of the box; The at least one speaker is connected to the waveform generator; The oscillation excitation signal drives the vibration element to generate the oscillating wave airflow, comprising: The at least one speaker receives the oscillation excitation signal generated by the waveform generator to generate the oscillating wave airflow.

17. The respiratory impedance measurement method according to claim 14, wherein: The “calculating the impedance of the subject's respiratory system based on the gas pressure signal and the gas flow signal” includes: performing denoising processing on the gas pressure signal and the gas flow signal; The quotient of the Fourier transform of the denoised gas pressure signal and the gas flow signal is calculated to obtain the impedance of the subject's respiratory system, wherein the impedance includes respiratory resistance and respiratory reactance.

18. The respiratory impedance measurement method according to claim 17, wherein: The method further comprises: A frequency impedance curve of the subject is displayed, wherein the frequency impedance curve includes a frequency resistance curve and a frequency reactance curve, the frequency resistance curve is obtained according to the respiratory resistance, and the frequency reactance curve is obtained according to the respiratory reactance.

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