CN218978907U - Respiratory impedance measurement system - Google Patents

Abstract

The utility model relates to the technical field of impedance measurement of human respiratory systems, in particular to a respiratory impedance measurement system. The respiratory impedance measurement system not only can accurately measure the impedance of the human respiratory system with a simple structure, but also can save the impedance to a local memory space and/or upload the impedance to a medical data management platform, so that the management such as the adjustment and the application of the impedance is more convenient and rapid, and the respiratory impedance measurement system is favorable for adapting to the development of big data age.

Description

Respiratory impedance measurement system

Technical Field

The utility model relates to the technical field of impedance measurement of human respiratory systems, in particular to a respiratory impedance measurement system.

Background

Currently, in order to check whether there is a lesion in the lung function of a person, it is necessary to measure the respiratory impedance of the person. However, in the existing impedance measurement equipment, system and method of the human respiratory system, the structure is often complex, only the impedance of the human respiratory system can be measured, the function is relatively single, and the development of the current big data age cannot be satisfied.

Disclosure of Invention

Aiming at the problems that the structure is complex, the large data age development is difficult to adapt to and the like in the existing impedance measuring equipment, system and method of the human respiratory system, the embodiment of the utility model provides a respiratory impedance measuring system.

The respiratory impedance measurement system provided by the embodiment of the utility model is used for measuring the impedance of a respiratory system of a subject and comprises an oscillation module, a connection module, a detection module and a calculation module, wherein the oscillation module is used for generating an oscillation wave airflow; the connecting module is connected with the oscillating module and is used for transmitting the oscillating wave airflow generated by the oscillating module to the subject and receiving the target respiratory airflow exhaled by the subject; the detection module is used for detecting the gas pressure and the gas flow of the target respiratory airflow in the connection module to respectively obtain a gas pressure signal and a gas flow signal; the computing module is connected with the detecting module and is used for computing the impedance of the respiratory system of the subject according to the gas pressure signal and the gas flow signal; the computing module is also used for storing the impedance to a local memory space and/or uploading the impedance to a medical data management platform according to the set result output mode.

According to the respiratory impedance measurement system and the respiratory impedance measurement method provided by the embodiment of the utility model, the impedance of the human respiratory system can be accurately measured by a simple structure, and can be stored in a local memory space and/or uploaded to the medical data management platform, so that the management such as the taking and application of the impedance is more convenient, and the respiratory impedance measurement system and the respiratory impedance measurement method are beneficial to adapting to the development of big data age.

Drawings

In order to more clearly illustrate the technical solution of the embodiments of the present utility model, the drawings that are needed in the description of the embodiments will be briefly described.

FIG. 1 is a schematic diagram of a respiratory impedance measurement system according to an embodiment of the present utility model;

FIG. 2 is a schematic diagram showing a part of the structure and components of the respiratory impedance measurement system according to an embodiment of the present utility model;

fig. 3 is a schematic structural diagram of a vibrating element in an oscillating module of a respiratory impedance measuring system according to an embodiment of the present utility model;

FIG. 4 is a schematic diagram of a respiratory impedance measurement system according to another embodiment of the present utility model;

FIG. 5 is a schematic view of the components and structure of a respiratory impedance measurement system according to another embodiment of the present utility model;

fig. 6 is a schematic structural diagram of a respiratory impedance measurement system according to another embodiment of the present utility model.

Detailed Description

The technical solutions in the embodiments of the present utility model will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present utility model.

It should be understood that the terms "comprises" and "comprising," when used in this specification and the appended claims, specify the presence of stated 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.

It is also to be understood that the terminology used in the description of the utility model herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the utility model. As used in this specification and the appended claims, the singular forms "a," "an," and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise.

It should be further understood that the term "and/or" as used in the present specification and the appended claims refers to any and all possible combinations of one or more of the associated listed items, and includes such combinations.

The terms "respiratory impedance", "impedance" and "respiratory impedance" as used herein are understood to mean the impedance of the respiratory system of the human body, which is an important indicator in the examination of lung function. It should be understood that the expressions "respiratory impedance", "impedance of the respiratory system" and "impedance of the respiratory system of the human body" as used herein are consistent and mutually generic.

Referring to fig. 1, fig. 1 is a schematic diagram illustrating a respiratory impedance measurement system according to an embodiment of the utility model.

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

The oscillation module 1 is used for generating an oscillating wave airflow.

The connection module 2 is connected to the oscillation module 1, and the connection module 2 is configured to transmit the oscillating wave airflow generated by the oscillation module 1 to the subject 5 and receive the target respiratory airflow exhaled by the subject 5.

The detecting module 3 is configured to detect the gas pressure and the gas flow of the target respiratory airflow in the connecting module 2, so as to obtain a gas pressure signal and a gas flow signal, respectively.

The calculating module 4 is connected with the detecting module 3, and the calculating module 4 is used for calculating the impedance of the respiratory system of the subject 5 according to the gas pressure signal and the gas flow signal; and the impedance is stored in a local memory space according to the set result output mode, and/or uploaded to a medical data management platform.

According to the embodiment of the utility model, the oscillating wave airflow is generated and applied to the spontaneous respiratory airflow of the subject 5, so that the corresponding oscillating wave airflow can be generated in the respiratory system of the subject 5, the intensity of the airflow inhaled by the subject 5 is enhanced, and the value related to the respiratory impedance in the respiratory airflow exhaled by the subject 5 after receiving the oscillating wave airflow is amplified, so that the gas pressure signal and the gas flow signal obtained by respectively detecting the gas pressure and the gas flow of the current airflow are also stronger, and the detection module 3 is arranged in the connection module 2, so that the gas pressure and the gas flow of the current airflow can be directly detected. Therefore, the respiratory impedance measurement system 100 provided in the embodiment of the present utility model can effectively detect the impedance of the respiratory system of the subject 5 with a simple structure, and after the impedance is measured, save the impedance to the local memory space, and upload the impedance to the medical data management platform for medical personnel to refer to and use for diagnosis, so that the impedance can be saved to the local memory space, and interaction between the respiratory impedance measurement system 100 and the medical data management platform can be realized, so that management such as the adjustment and application of the impedance is more convenient, and the development of the big data age is facilitated.

The medical data management platform may be a platform located at a server end and used for collecting and managing medical data, and medical staff may manage the medical data uploaded by the respiratory impedance measurement system 100 or other medical detection devices located in various places through the medical data management platform, and diagnose a patient according to the corresponding medical data, where the medical data includes the impedance.

The oscillating wave air flow is a single frequency or a complex frequency oscillating wave air flow, and when the oscillating wave air flow is a single frequency oscillating wave air flow, the oscillating wave air flow is a sine wave air flow, and when the oscillating wave air flow is a complex frequency oscillating wave air flow, the oscillating wave air flow is a pulse wave air flow. The frequency of the oscillating wave air flow is 3-50 Hz no matter the oscillating wave air flow is single frequency or compound frequency.

The gas pressure signal is a detected gas pressure versus time curve of the target respiratory airflow, and the gas flow signal is a detected gas flow versus time curve of the target respiratory airflow.

The result output mode includes simultaneously saving the impedance to a local memory space and uploading the impedance to a medical data management platform, saving the impedance only to the local memory space, and uploading the impedance only to the medical data management platform. The result output mode can be preset default setting or user selection setting.

In some embodiments, one end of the connection module 2 is connected to the oscillation module 1, and the other end of the connection module 2 is configured to extend into the oral cavity of the subject 5 when measuring the impedance of the respiratory system of the subject 5, and the connection module 2 is configured to transmit the oscillating wave airflow generated by the oscillation module 1 to the subject 5 and to receive the target respiratory airflow exhaled by the subject 5 after the oscillating wave airflow is applied.

In some embodiments, the detection module 3 is disposed in the connection module 2, so that the gas pressure signal and the gas flow signal of the target respiratory airflow transmitted in the connection module 2 can be directly detected to obtain the gas pressure signal and the gas flow signal, respectively. In other embodiments, the detecting module 3 may be disposed outside the connecting module 2, for example, at a connection between the detecting module 3 and the calculating module 4 or between the detecting module and the oscillating module 1, so that the gas pressure and the gas flow of the target respiratory airflow may be detected to obtain the gas pressure signal and the gas flow signal, respectively. The detection module 3 samples and detects the gas pressure and the gas flow rate of the target respiratory airflow through a sampling tube connected to the connection module 2 to obtain the gas pressure signal and the gas flow rate signal, respectively.

In some embodiments, the computing module 4 computes the impedance of the respiratory system of the subject 5 from the gas pressure signal and the gas flow signal, comprising: the calculation module 4 performs denoising processing on the gas pressure signal and the gas flow signal respectively; the calculation module 4 calculates a quotient of fourier transform of the denoised gas pressure signal and the gas flow signal to obtain an impedance of the respiratory system of the subject 5, wherein the impedance includes respiratory resistance and respiratory reactance.

In some embodiments, the respiratory impedance measurement system 100 may include a memory (not shown), and the computing module 4 may store the impedance in the local memory space, which may mean that the impedance is stored in the memory.

Referring to fig. 2, fig. 2 is a schematic diagram illustrating a part of the respiratory impedance measurement system 100 according to an embodiment of the utility model.

The oscillation module 1 includes a waveform generator 11 and a vibration element 12, the vibration element 12 is connected between the connection module 2 and the waveform generator 11, the waveform generator 11 is used for generating an oscillation excitation signal with a single frequency or a composite frequency, and the vibration element 12 is used for generating the oscillation wave airflow under the driving of the oscillation excitation signal.

Further, the oscillatory wave air flow generated by the vibrating element 12 is transmitted to the subject 5 through the connection module 2.

Referring to fig. 3, fig. 3 is a schematic structural diagram of the vibration element 12 in the oscillation module of the respiratory impedance measurement system 100 according to an embodiment of the present utility model, wherein (a) in fig. 3 is a left side view of the vibration element 12, (B) in fig. 3 is a front view of the vibration element 12, (C) in fig. 3 is a bottom view of the vibration element 12, and (D) in fig. 3 is a three-dimensional perspective view of the vibration element 12.

The vibration element 12 includes at least one speaker 121 and a case 122.

The case 122 has an outer surface and a cavity surrounded by the outer surface, and the outer surface of the case 122 is provided with an air outlet.

The at least one speaker 121 is disposed through an outer surface of the case 122, and an acoustic outlet of the at least one speaker 121 is disposed in a cavity of the case 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 and generate the oscillation wave air stream.

Wherein the gas outlet is connected with the connecting module 2. Thus, the speaker air flows generated in the at least one speaker 121 are combined in the cavity, and the oscillatory wave air flow is finally generated and output to the connection module 2 through the air flow output port.

In some embodiments, the airflow outlet is provided in the outer surface of the housing 122 on a side remote from the at least one speaker 121.

In other embodiments, the housing 122 is a polyhedron, and the number of faces of the housing 122 is greater than the number of the at least one speaker 121; each speaker 121 is respectively disposed in different surfaces of the case 122, and the air outlet is disposed on a surface of the case 122, where the speaker 121 is not disposed.

Fig. 3 (B) is a front view of the case 122 on which the speaker 121 is not provided, fig. 3 (a) is a left side view of the case 122 on which the speaker 121 is not provided, and fig. 3 (C) is a bottom view of the case 122 on which the speaker 121 is not provided.

The foregoing speaker airflow is also an oscillating wave airflow with a single frequency or a composite frequency, and the present embodiment provides a vibrating element 12, where by setting a box 122, the vibrating element 12 may integrate a plurality of small-sized speakers 121, so that diaphragms in the plurality of speakers 121 vibrate simultaneously to generate a larger speaker airflow, and finally the vibrating airflow is converged into the box 122 to have a stronger oscillating wave airflow, which is not only beneficial to reducing the size of equipment, but also beneficial to improving the detection quality.

Wherein the speaker airflow generated in each speaker 121 is the same, and the frequency of the aforementioned speaker airflow coincides with the frequency of the aforementioned oscillatory wave airflow. The greater the number of speakers 121 connected to the waveform generator 11, the stronger the intensity of the oscillatory wave air flow that is collected by the speaker air flow in the case 122.

With continued reference to fig. 2, in other embodiments, the vibration element 12 includes a turbine mounted on the connection module 2, and a driving motor connected between the turbine and the waveform generator 11, and configured to receive the oscillation excitation signal generated by the waveform generator 11 and drive the turbine to rotate so as to generate the oscillating wave airflow. The turbine generates the oscillatory wave air flow with a certain frequency under the drive of the oscillation excitation signal, and the oscillatory wave air flow generated by the turbine is determined by the oscillation excitation signal. The oscillatory wave air flow generated by the turbine flows through the connection module 2 and is transmitted to the subject 5 through the connection module 2.

With continued reference to fig. 2, in still other embodiments, the vibration element 12 includes a gas storage assembly and a gas valve coupled to a gas outlet in the gas storage assembly, the gas valve alternately opening and closing in response to the oscillation excitation signal.

Specifically, compressed air is stored in the air storage assembly, the air storage assembly comprises a compressed air output port, the compressed air output port is in sealing connection with the connection module 2, the air valve is arranged at the compressed air output port and is connected with the waveform generator 11 and is used for receiving the oscillation excitation signal generated by the waveform generator 11, and the air valve is alternately opened and closed in response to the oscillation excitation signal, so that the compressed air in the air storage assembly is driven to intermittently enter the connection module 2 through the opened air valve to generate the oscillation wave air flow.

With continued reference to fig. 2, the connection module 2 includes a measurement interface 21 and a gas pipe 22, wherein a first end a of the gas pipe 22 is connected to the vibration element 12 in the vibration module 1, and a second end b is connected to the measurement interface 21. Wherein, the measuring interface 21 is used for extending into the oral cavity of the subject 5 when measuring the impedance of the respiratory system of the subject 5; the gas pipe 22 is used for transmitting the oscillatory wave airflow generated by the oscillatory wave generator 1 to the subject 5 and receiving the target respiratory airflow when measuring the impedance of the respiratory system of the subject 5. Wherein the receiving of the target respiratory airflow by the gas conduit 22 means that the target respiratory airflow exhaled by the subject 5 after the application of the oscillatory wave airflow finally flows out through the gas conduit 22. The gas pipe 22 is a hollow pipe.

In some embodiments, as previously described, the vibration element 12 includes the at least one speaker 121 and the housing 122. The gas flow outlet on the outer surface of the housing 122 is connected to the first end a of the gas pipe 22. Thus, the speaker air flows generated in the at least one speaker 121 are combined in the cavity, and the oscillatory wave air flow is finally generated and output to the air duct 22 through the air flow output port.

As described above and shown in fig. 2, in some embodiments, the detection module 3 is disposed in the gas pipeline 22, so that when the target respiratory airflow exhaled by the subject 5 after the oscillatory wave airflow is applied flows through the gas pipeline 22, the detection module 3 can detect the gas pressure and the gas flow of the target respiratory airflow to obtain the gas pressure signal and the gas flow signal, respectively.

The connection module 2 further includes a high-frequency blocking component, one end of the high-frequency blocking component is communicated with the gas pipeline 22, and the other end of the high-frequency blocking component is communicated with the outside air, so as to realize gas circulation inside and outside the gas pipeline 22 and block the oscillatory wave airflow from flowing out.

In some embodiments, the high frequency blocking assembly includes a pipe branch 23 and a screen (not shown), the pipe branch 23 is in communication with the gas pipe 22, and the pipe branch 23 is used to enable external air to flow into the gas pipe 22 for the respiration of the subject 5 when the impedance of the respiratory system of the subject 5 is measured; the screen (not shown) is disposed at the junction c between the pipe branch 23 and the gas pipe 22, and the aperture of each mesh in the screen (not shown) is relatively small, for example, in the order of micrometers to millimeters, and the oscillatory wave gas flow in the gas pipe 22 cannot flow into the air from the pipe branch 23 through the screen (not shown) due to the diffraction effect of the oscillatory wave, but the air, which is not affected by the low frequency gas flow, enters the gas pipe 22 through the screen (not shown) for the respiration of the subject 5. Therefore, the high frequency blocking assembly not only allows the external air to flow into the gas duct 22 for the subject 5 to breathe, but also prevents the oscillatory wave air flow from flowing out into the air, i.e., the high frequency blocking assembly can realize the gas circulation inside and outside the gas duct 22 and block the oscillatory wave air flow from flowing out.

In other embodiments, the high frequency blocking assembly comprises an elongated curved conduit in communication with the gas conduit 22, and the elongated curved conduit has a relatively small diameter, e.g., the elongated curved conduit may have a diameter on the order of millimeters, such that the oscillatory wave gas flow in the gas conduit 22 cannot flow from the conduit branch 23 to the air through the elongated curved conduit due to diffraction of oscillatory wave, but air that is not affected by low frequency flow is allowed to pass through the elongated curved conduit into the gas conduit 22 for respiration by the subject 5. Thus, the elongated curved pipe in the high frequency blocking assembly can realize the gas circulation inside and outside the gas pipe 22, and block the oscillatory wave gas flow from flowing out.

In some embodiments, the connection module 2 further includes a filter 24, where the filter 24 is installed in the gas pipe 22 near the second end b, that is, near the measurement interface 21, and the filter 24 is used to isolate contaminants and prevent cross infection of the subject 5 during use.

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

Referring to fig. 4 and fig. 5 together, fig. 4 is a schematic diagram illustrating the composition of the respiratory impedance measurement system 100 according to another embodiment of the utility model, and fig. 5 is a schematic diagram illustrating the structure of the support module of the respiratory impedance measurement system 100 according to another embodiment of the utility model.

The respiratory impedance measuring system 100 includes a support module 6 (see fig. 1) in addition to the oscillation module 1, the connection module 2, the detection module 3, and the calculation module 4, wherein the support module 6 is connected to the connection module 2, and is configured to support cheeks of the subject 5 when measuring the impedance of the respiratory system of the subject 5.

As shown in fig. 5, the support module 6 includes a V-shaped support member and a driving mechanism, the measurement interface 21 is disposed through a tip of the V-shaped support member, and the driving mechanism is connected to the V-shaped support member to adjust an included angle of the V-shaped support member to adapt to a cheek of the subject 5, so as to support the cheek of the subject 5 when measuring an impedance of a respiratory system of the subject 5.

With continued reference to fig. 2 or fig. 5, in some embodiments, the detecting module 3 includes a pressure sensor and a flow sensor, where the pressure sensor and the flow sensor are respectively disposed at d and e of the gas pipe 22 and are both connected to the calculating module 4, the pressure sensor is used for detecting the gas pressure in the connecting module 2 to obtain the gas pressure signal, and the flow sensor is used for detecting the gas flow in the connecting module 2 to obtain the gas flow signal.

It should be appreciated that the pressure sensor and the flow sensor should be disposed in the gas conduit 22 as close to the measurement port 21 as possible, and the pressure sensor should be disposed in the gas conduit 22 closer to the measurement port 21 than the flow sensor to detect the accurate gas pressure and gas flow of the target respiratory gas flow.

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

As previously described, in some embodiments, the computing module 4 computes the impedance of the respiratory system of the subject 5 from the gas pressure signal and the gas flow signal, comprising: the calculation module 4 performs denoising processing on the gas pressure signal and the gas flow signal respectively; the calculation module 4 calculates a quotient of fourier transform of the denoised gas pressure signal and the gas flow signal to obtain an impedance of the respiratory system of the subject 5, wherein the impedance includes respiratory resistance and respiratory reactance.

The denoising process includes: and removing a low-frequency spontaneous breathing signal from the gas pressure signal and the gas flow signal as noise, respectively, to extract a gas pressure signal and a gas flow signal caused by the oscillatory wave gas flow.

The calculation formula of the aforementioned "calculating the quotient of the fourier transform of the gas pressure signal and the gas flow signal after the noise reduction processing, to obtain the impedance of the respiratory system of the subject 5" is: z (F) =p (F)/F (F) =r (F) +jx (F), wherein Z (F) represents the impedance, P (F) represents a fourier transform function of the denoised gas pressure signal, F (F) represents a fourier transform function of the denoised gas flow signal, R (F) represents the respiratory resistance, and X (F) represents the respiratory reactance, and reflects the compliance of the peripheral lung tissue and the thorax.

Referring to fig. 6, fig. 6 is a schematic structural diagram of the respiratory impedance measurement system 100 according to another embodiment of the utility model.

In some embodiments, as shown in fig. 6, the respiratory impedance measurement system 100 further includes a display module 7, where the display module 7 is connected to the computing module 4, and the display module 7 is configured to display a frequency impedance curve of the subject 5 according to the impedance calculated by the computing module 4, where 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.

While the utility model has been described with reference to certain preferred embodiments, it will be understood by those skilled in the art that various changes and substitutions of equivalents may be made and equivalents will be apparent to those skilled in the art without departing from the scope of the utility model. Therefore, the protection scope of the utility model is subject to the protection scope of the claims.

Claims (12)

1. A respiratory impedance measurement system for measuring an impedance of a respiratory system of a subject, the respiratory impedance measurement system comprising:

the oscillation module is used for generating an oscillating wave airflow;

the connecting module is connected with the oscillating module and is used for transmitting the oscillating wave airflow generated by the oscillating module to a subject and receiving target respiratory airflow exhaled by the subject;

the detection module is used for detecting the gas pressure and the gas flow of the target respiratory airflow in the connection module to respectively obtain a gas pressure signal and a gas flow signal; and

the computing module is connected with the detecting module and is used for storing the impedance of the respiratory system of the subject, which is obtained by computing according to the gas pressure signal and the gas flow signal, into a local memory space according to a set result output mode and/or uploading the impedance to a medical data management platform;

the vibration module comprises a waveform generator and a vibration element, wherein the vibration element is connected between the connection module and the waveform generator, the waveform generator is used for generating an oscillation excitation signal with single frequency or composite frequency, and the vibration element is used for generating the oscillation wave airflow under the driving of the oscillation excitation signal.

2. The respiratory impedance measurement system according to claim 1, wherein the vibrating element comprises a housing and at least one speaker;

the box body is provided with an outer surface and a cavity formed by encircling the outer surface, and the outer surface of the box body is provided with an air flow output port;

the at least one loudspeaker penetrates through the outer surface of the box body, and the sound outlet of the at least one loudspeaker is arranged in the cavity of the box body; the at least one loudspeaker is connected with the waveform generator to receive the oscillation excitation signal generated by the waveform generator and generate the oscillation wave airflow.

3. The respiratory impedance measurement system according to claim 2, wherein the airflow outlet is provided in an outer surface of the housing on a side remote from the at least one speaker.

4. The respiratory impedance measurement system according to claim 2, wherein the housing is a polyhedron, the number of faces of the housing being greater than the number of the at least one speaker; each loudspeaker is respectively arranged in different surfaces of the box body in a penetrating way, and the air flow output port is arranged on one surface of the outer surface of the box body, on which the loudspeaker is not arranged.

5. The respiratory impedance measurement system according to claim 2, wherein the vibration element comprises a turbine, a drive motor, the connection module comprising a gas conduit, the turbine being mounted at a first end of the gas conduit, the drive motor being connected between the turbine and the waveform generator, the drive motor being configured to receive the oscillating excitation signal generated by the waveform generator and to drive the turbine to rotate so as to generate the oscillating wave air stream.

6. The respiratory impedance measurement system of claim 1, wherein the vibrating element comprises a gas storage assembly and a gas valve coupled to a gas outlet in the gas storage assembly, the gas valve alternately opening and closing in response to the oscillation excitation signal.

7. The respiratory impedance measurement system according to claim 1, wherein the connection module comprises a measurement interface and a gas conduit, a first end of the gas conduit being connected to the vibrating element in the oscillation module and a second end being connected to the measurement interface.

8. The respiratory impedance measurement system according to claim 7, wherein the connection module further comprises a high frequency blocking assembly, one end of the high frequency blocking assembly is communicated with the gas pipeline, and the other end of the high frequency blocking assembly is communicated with the outside air, so as to enable gas circulation inside and outside the gas pipeline and block the oscillatory wave gas flow from flowing out.

9. The respiratory impedance measurement system according to claim 7, further comprising a support module coupled to the connection module for supporting the cheeks of the subject when measuring the impedance of the respiratory system of the subject.

10. The respiratory impedance measurement system according to claim 9, wherein the support module comprises a V-shaped support and a drive mechanism, wherein the measurement interface extends through a tip of the V-shaped support, and wherein the drive mechanism is coupled to the V-shaped support to adjust an included angle of the V-shaped support to fit a cheek of the subject.

11. The respiratory impedance measurement system according to claim 7, wherein the detection module comprises a pressure sensor and a flow sensor, wherein the pressure sensor and the flow sensor are both disposed in the gas conduit and are both connected to the calculation module, wherein the pressure sensor is configured to detect a gas pressure in the connection module to obtain the gas pressure signal, and wherein the flow sensor is configured to detect a gas flow in the connection module to obtain the gas flow signal.

12. The respiratory impedance measurement system of claim 1, wherein the computing module computes an impedance of a respiratory system of the subject from the gas pressure signal and the gas flow signal, comprising:

the calculation module carries out denoising treatment 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 noise removal processing to obtain the impedance of the respiratory system of the subject, wherein the impedance comprises respiratory resistance and respiratory reactance.

Images