Automatic detection and calibration system, method and device for lung function instrument and medium

Abstract

The invention discloses an automatic detection and calibration system, method and device for a lung function instrument and a medium, and the method comprises the steps: detecting whether the installation state of a pressure difference measurement airway or a muscle force measurement airway on a housing is normal or not in response to the starting operation of a user on the lung function instrument; when it is detected that the installation state of the differential pressure measurement air channel or the muscle force measurement air channel is abnormal, an alarm instruction is sent out; when it is detected that the installation state of the pressure difference measuring airway or the muscle force measuring airway is normal, whether the power supply state of a power supply system of the lung function instrument is normal or not is obtained; when it is detected that the power supply system supplies power abnormally, the power supply system is cut off and an alarm instruction is sent; when it is detected that the power supply system supplies power normally, whether the power-on state of electric equipment of the pulmonary function instrument is normal or not is detected; when it is detected that any electric device is powered on abnormally, an alarm instruction is sent out; and when it is detected that all the electric devices are normally powered on, automatic detection calibration is ended, and an automatic calibration process is started.

Description

Technical Field

[0001] The present invention relates to the technical field of pulmonary function instruments, and particularly to an automatic detection and calibration system, method, device and medium for a pulmonary function instrument. Background Art

[0002] A pulmonary function instrument is a medical device used to measure the volume of air inhaled and exhaled by the lungs. It can perform pulmonary function tests and track the health of the lungs. It can measure common pulmonary function detection parameters such as FVC (forced vital capacity), FEV1 (forced expiratory volume in one second), FEV1 / FVC (one-second rate, the ratio of forced expiratory volume in one second to forced vital capacity), etc. Through the detection of the pulmonary function instrument, doctors can timely detect lung diseases or injuries, such as asthma, chronic obstructive pulmonary disease, etc., and understand the development of the disease, providing important references for doctors, helping to formulate and adjust treatment plans, and monitoring the treatment effect.

[0003] During the long-term use of a pulmonary function detector, measurement errors may occur due to environmental factors, aging of internal components, etc. Therefore, it is necessary to know the internal state of the pulmonary function detector in advance before the detection to prevent measurement errors. Summary of the Invention

[0004] Embodiments of the present application provide a method, device, system and medium for automatic detection and calibration of a pulmonary function instrument, which solve the technical problem in the prior art of lacking a way to know the internal state of a pulmonary function detector to prevent measurement errors.

[0005] To solve the above technical problem, in a first aspect, embodiments of the present application provide an automatic detection and calibration system for a pulmonary function instrument. The pulmonary function instrument includes a housing, and a first measurement airway and a second measurement airway are arranged inside the housing. The first measurement airway is connected to a differential pressure sensor, and the second measurement airway is connected to a muscle strength sensor;

[0006] The housing allows a differential pressure measurement airway or a muscle strength measurement airway to penetrate. A differential pressure collection tube is arranged on the differential pressure measurement airway, and a muscle strength collection tube is arranged on the muscle strength measurement airway;

[0007] When the differential pressure measurement airway penetrates inside the housing, the differential pressure collection tube communicates with the first measurement airway to measure the expiratory differential pressure and / or the inspiratory differential pressure; when the muscle strength measurement airway penetrates inside the housing, the muscle strength collection tube communicates with the second measurement airway to measure the muscle strength;

[0008] It further includes a power supply system for power supply.

[0009] Furthermore, the system includes a first thin film piezoelectric sheet arranged on the first measurement airway and a second thin film piezoelectric sheet arranged on the second measurement airway;

[0010] When the differential pressure measuring air duct is arranged in the housing, the differential pressure collecting pipe is butted against the first measuring air duct and abuts against the first thin film piezoelectric sheet.

[0011] When the muscle strength measuring air duct is arranged in the housing, the muscle strength collecting pipe is butted against the second measuring air duct and abuts against the second thin film piezoelectric sheet.

[0012] Furthermore, the system further includes a first temperature sensor for detecting the ambient temperature and a second temperature sensor for detecting the temperature of the gas to be detected in the differential pressure sensor.

[0013] The system further includes an alarm and a controller. The signal input end of the controller is respectively connected to the first thin film piezoelectric sheet, the second thin film piezoelectric sheet, the first temperature sensor, and the second temperature sensor, and is respectively used for receiving signals. The signal output end of the controller outputs a control signal, and the control signal is used to control the alarm and the pulmonary function instrument.

[0014] In a second aspect, an embodiment of the present application provides an automatic detection and calibration method for a pulmonary function instrument. The method includes:

[0015] In response to the user's operation of turning on the pulmonary function instrument, detecting whether the installation state of the differential pressure measuring air duct or the muscle strength measuring air duct on the housing is normal;

[0016] When it is detected that the installation state of the differential pressure measuring air duct or the muscle strength measuring air duct is abnormal, an alarm instruction is issued; when it is detected that the installation state of the differential pressure measuring air duct or the muscle strength measuring air duct is normal, obtaining whether the power supply state of the power supply system of the pulmonary function instrument is normal:

[0017] When it is detected that the power supply of the power supply system is abnormal, the power supply system is cut off and an alarm instruction is issued; when it is detected that the power supply of the power supply system is normal, detecting whether the power-on state of the electrical equipment of the pulmonary function instrument is normal;

[0018] When it is detected that any electrical equipment is powered on abnormally, an alarm instruction is issued; when it is detected that all electrical equipment is powered on normally, the automatic detection and calibration is ended and the automatic calibration process is started.

[0019] Furthermore, detecting whether the installation state of the differential pressure measuring air duct or the muscle strength measuring air duct on the housing is normal specifically includes:

[0020] Respectively obtaining the real-time voltages output by the first thin film piezoelectric sheet and the second thin film piezoelectric sheet;

[0021] Based on the real-time voltages, determining whether the installation state of the differential pressure measuring air duct or the muscle strength measuring air duct on the housing is normal.

[0022] Further, the automatic calibration process includes:

[0023] Obtain the ambient temperature T 0 ;

[0024] Obtain the gas temperature T of the gas to be measured in the differential pressure sensor 1 ;

[0025] When T 0 ≠T 1 , perform temperature compensation on the expiratory pressure difference and / or inspiratory pressure difference detected by the spirometer.

[0026] Further, the temperature compensation for the expiratory pressure difference and / or inspiratory pressure difference detected by the spirometer specifically includes:

[0027] Perform temperature compensation on the expiratory pressure difference and / or inspiratory pressure difference based on the temperature drift curve, that is: ΔP = f(T 0 ) - f(T 1 ), where ΔP is the compensation amount of the expiratory pressure difference and / or inspiratory pressure difference, and f(x) is the temperature drift curve.

[0028] In a third aspect, an embodiment of the present application provides a spirometer automatic detection and calibration device, and the device includes:

[0029] A first detection module, configured to detect whether the installation state of the differential pressure measurement airway or the muscle strength measurement airway on the housing is normal in response to the user's power-on operation of the spirometer;

[0030] A second detection module, configured to issue an alarm instruction when detecting that the installation state of the differential pressure measurement airway or the muscle strength measurement airway is abnormal; when detecting that the installation state of the differential pressure measurement airway or the muscle strength measurement airway is normal, obtain whether the power supply state of the power supply system of the spirometer is normal;

[0031] A third detection module, configured to cut off the power supply system and issue an alarm instruction when detecting that the power supply of the power supply system is abnormal; when detecting that the power supply of the power supply system is normal, detect whether the power-on state of the electrical equipment of the spirometer is normal;

[0032] A fourth detection module, configured to issue an alarm instruction when detecting that any electrical equipment is powered on abnormally; when detecting that all electrical equipment is powered on normally, end the automatic detection and calibration and start the automatic calibration process.

[0033] Fourthly, an embodiment of the present application provides an automatic detection and calibration device for a spirometer, including a memory, a processor, and a computer program stored on the memory and executable on the processor. It is characterized in that when the processor executes the program, the method described in any item of the second aspect is implemented.

[0034] Fifthly, an embodiment of the present application provides a computer-readable storage medium, on which a computer program is stored. When the program is executed by a processor, the method described in any item of the second aspect is implemented.

[0035] One or more technical solutions provided in the embodiments of the present application have at least the following technical effects or advantages:

[0036] (1) Eliminate errors and improve accuracy

[0037] During the long-term use of a spirometer, measurement errors may occur due to environmental factors, aging of internal components, etc. The automatic detection and calibration method, device, system, and medium for the spirometer described in the embodiments of the present application can detect and correct these errors in a timely manner through automatic detection and calibration, ensuring the accuracy of the measurement results.

[0038] (2) Adapt to environmental changes and maintain comparability

[0039] The parameters measured by a spirometer are greatly affected by the environment, such as temperature. The automatic detection and calibration method, device, system, and medium for the spirometer described in the embodiments of the present application can perceive environmental changes in real time and make corresponding adjustments to the measurement results, making the measurement results comparable and facilitating doctors' diagnosis and treatment.

[0040] (3) Ensure the coordinated operation of software and hardware and improve reliability

[0041] The software and hardware of a spirometer need to work closely together to ensure the accuracy of the measurement results. The automatic detection and calibration method, device, system, and medium for the spirometer described in the embodiments of the present application can detect the connection status between the software and hardware, ensuring the accuracy and stability of data transmission, thereby improving the reliability of the device.

[0042] (4) Meet industry standards and regulatory requirements

[0043] As a medical device, a spirometer needs to meet certain industry standards and regulatory requirements. The automatic detection and calibration method, device, system, and medium for the spirometer described in the embodiments of the present application can ensure that the device complies with relevant standards and regulations, providing compliant spirometry services for medical institutions.

[0044] (5) Improve detection efficiency and accuracy

[0045] The automatic detection and calibration method, device, system and medium of the spirometer described in the embodiments of the present application can greatly shorten the calibration time and improve the detection efficiency through an automated detection and calibration process; at the same time, the automated calibration process also reduces the errors caused by manual operations and improves the accuracy of calibration.

[0046] In summary, the automatic detection and calibration method, device, system and medium of the spirometer described in the embodiments of the present application are of great significance for ensuring the accuracy, reliability and consistency of the measurement results of the spirometer and are an indispensable part of the spirometer. BRIEF DESCRIPTION OF THE DRAWINGS

[0047] Figure 1 Partial structure explosion of a spirometer in an embodiment of the present invention Figure 1 ;

[0048] Figure 2 Schematic diagram of the overall structure of a spirometer when installing a differential pressure measurement airway in an embodiment of the present invention;

[0049] Figure 3 Side view of a spirometer when installing a differential pressure measurement airway in an embodiment of the present invention;

[0050] Figure 4 Front view of a spirometer when installing a differential pressure measurement airway in an embodiment of the present invention;

[0051] Figure 5 Partial structure diagram of a spirometer when installing a differential pressure measurement airway in an embodiment of the present invention;

[0052] Figure 6 Cross-sectional view of a spirometer when installing a differential pressure measurement airway in an embodiment of the present invention;

[0053] Figure 7 Partial structure diagram of a spirometer when installing a muscle strength measurement airway in an embodiment of the present invention;

[0054] Figure 8 Cross-sectional view of a spirometer when installing a muscle strength measurement airway in an embodiment of the present invention;

[0055] Figure 9 Partial structure explosion of a spirometer in an embodiment of the present invention Figure 2 。

[0056] Figure 10 Flow chart of an automatic detection and calibration method for a spirometer in an embodiment of the present invention;

[0057] Figure 11Schematic diagram of the structure of an automatic detection and calibration device for a pulmonary function instrument in an embodiment of the present invention:

[0058] Figure 12 Schematic diagram of the structure of another automatic detection and calibration device for a pulmonary function instrument in an embodiment of the present invention. Specific implementation manners

[0059] By providing an automatic detection and calibration method, device, system and medium for a pulmonary function instrument in an embodiment of the present application, the technical problem in the prior art of lacking a way to know the internal state of a pulmonary function detector to prevent measurement errors is solved.

[0060] To better understand the above technical solution, the above technical solution will be described in detail below in conjunction with the accompanying drawings of the specification and specific implementation manners.

[0061] Embodiment 1

[0062] As Figure 1 shown, this embodiment discloses a pulmonary function instrument, and the pulmonary function instrument includes a housing, and the housing includes a rear cover 1 and a handle cover 2 that are buckled together. As Figure 2 shown, taking the direction of the pulmonary function instrument in the usage state as the standard, a perforation 29 is provided at the upper end of the housing, and the perforation 29 transversely (i.e., in the front-back direction from the handle cover 2 to the rear cover 1) penetrates through the handle cover 2 and the rear cover 1, and the perforation 29 is used for threading a differential pressure measurement airway 3 or a muscle strength measurement airway 21.

[0063] As Figures 2 - 6As shown in the figure, the differential pressure measurement air passage 3 is in the shape of a hollow cylindrical tube. The differential pressure measurement air passage 3 is used to detect the expiratory differential pressure or the inspiratory differential pressure. The two ends of the differential pressure measurement air passage 3 in the front-back direction are through. Its front end forms a first exhalation port a1, and the rear end forms a first air outlet b1. A filter mesh 33 extending along its own cross-section is provided inside the differential pressure measurement air passage 3. On the front and rear sides of the filter mesh 33 outside the differential pressure measurement air passage 3, a first collection tube 10 and a second collection tube 23 are respectively fixed. The first collection tube 10 and the second collection tube 23 both extend along the radial direction of the differential pressure measurement air passage 3. And the upper end of the first collection tube 10 is communicated with the differential pressure measurement air passage 3 on the front side of the filter mesh 33, and the upper end of the second collection tube 23 is communicated with the differential pressure measurement air passage 3 on the rear side of the filter mesh 33, that is, the first collection tube 10 is adjacent to the first exhalation port a1, and the second collection tube 23 is adjacent to the first air outlet b1. The lower end of the first collection tube 10 is used to communicate with the first connecting tube 11 described below, and the lower end of the second collection tube 23 is used to communicate with the second connecting tube 34 described below; because the filter mesh 33 is arranged in the differential pressure measurement air passage 3, when the gas passes through the filter mesh 33, blocked by the filter mesh 33, a differential pressure will be formed on the front and rear sides of the filter mesh 33. Among them, the first collection tube 10 and the second collection tube 23 are both the differential pressure collection tubes.

[0064] As Figures 7 - 8 As shown in the figure, the muscle strength measurement air passage 21 is in the shape of a hollow tube. The muscle strength measurement air passage 21 is used to detect the muscle strength value. The two ends of the muscle strength measurement air passage 21 in the front-back direction are through. Its front end forms a second exhalation port a2, and the rear end forms a second air outlet b2. A third collection tube 24 extending along its own radial direction is fixed on the outer wall of the differential pressure measurement air passage 3. The upper end of the third collection tube 24 is communicated with the muscle strength measurement air passage 21, and the lower end is used to communicate with the third connecting tube described below. Among them, the third collection tube 24 is the muscle strength collection tube.

[0065] A transfer seat 7 is arranged inside the housing (that is, inside the housing cavity, the same below). The transfer seat 7 can be fixed inside the rear cover 1. For example, a frame body is arranged inside the housing cavity, and the transfer seat 7 is erected on the frame body. Inside the transfer seat 7, a first transfer tube 35, a third transfer tube 37, and a second transfer tube 36 that are vertically through are arranged in sequence from front to back.

[0066] Wherein: The first collection tube 10 is connected to the upper end of the first adapter tube 35, and the lower end of the first adapter tube 35 is connected to one end of the differential pressure sensor 12 through the first connecting tube 11; The second collection tube 23 is connected to the upper end of the second adapter tube 36, and the lower end of the second adapter tube 36 is connected to the other end of the differential pressure sensor through the second connecting tube 34 to detect the differential pressure between the first collection tube 10 and the second collection tube 23. The third collection tube 24 is connected to the upper end of the third adapter tube 37, and the lower end of the third adapter tube 37 is connected to the muscle force sensor 22 through the third connecting tube to detect the muscle force. Among them, the differential pressure sensor 12 and the muscle force sensor 22 are respectively connected to the microprocessor 14. The differential pressure sensor 12, the muscle force sensor 22 and the microprocessor 14 are all arranged inside the housing cavity. The microprocessor 14 receives and processes the data detected by the differential pressure sensor 12 and the muscle force sensor 22, and calculates the expiratory differential pressure, the inspiratory differential pressure or the muscle force. Among them, the connected first adapter tube 35, the first connecting tube 11, and the connected second adapter tube 36, the second connecting tube 34 are all the first measurement airways. The third adapter tube 37 and the third connecting tube are the second measurement airways.

[0067] In addition, as Figure 5 , 7 shown, the input end of the microprocessor 14 is electrically connected to a power supply battery 13, the output end of the microprocessor 14 is fixedly connected to a terminal block 15, the front end of the terminal block 15 is fixedly connected to a plurality of control buttons 6, and the control buttons 6 are fixedly connected to the outer wall of the lower side of the handle cover 2. The control buttons 6 can be used to control the operation or shutdown of components such as the microprocessor 14, the first muscle force sensor 12, the second muscle force sensor, and the muscle force sensor 22. In addition, different control buttons 6 correspond to different detection functions and can be selected and used according to the required detection data. For example, in an embodiment of the present application, the control buttons 6 include three. One of them is a differential pressure measurement button for controlling the differential pressure sensor 12 to operate, another is a muscle force measurement button for controlling the muscle force sensor 22 to operate, and the other can be a switch button.

[0068] Therefore, when it is necessary to detect the expiratory pressure difference and / or the inspiratory pressure difference, insert the pressure difference measurement airway 3 into the perforation 29. When detecting the expiratory pressure difference, the user presses the pressure difference measurement button and then blows air into the first exhalation port a1. A part of the exhaled air passes through the first collection tube 10 and the first connection tube 11 and leads to the pressure difference sensor 12, another part passes through the filter mesh 33 and then through the second collection tube 23 and the second connection tube 34 and leads to the pressure difference sensor 12, and still another part is directly discharged from the first air outlet b1. The pressure difference sensor 12 sends the acquired pressure difference data to the microprocessor 14, and the microprocessor 14 obtains the expiratory pressure difference based on the pressure difference data and displays it on the display screen 5. When detecting the inspiratory pressure difference, the user inhales through the first exhalation port a1. After the air enters the pressure difference measurement airway 3 from the first air outlet b1, a part of it enters the user's body through the first exhalation port a1 for breathing, a part passes through the second collection tube 23 and the second connection tube 34 and leads to the pressure difference sensor 12, and still another part passes through the filter mesh 33 and then through the first collection tube 10 and the first connection tube 11 and leads to the pressure difference sensor 12. The pressure difference sensor 12 sends the acquired pressure difference data to the microprocessor 14, and the microprocessor 14 calculates the inspiratory pressure difference based on the pressure difference data and displays it on the display screen 5.

[0069] When it is necessary to measure muscle strength, insert the muscle strength measurement airway 21 into the perforation 29. The user presses the muscle strength measurement button and blows air through the second exhalation port a2. A part of the exhaled air is discharged from the second air outlet b2, and another part passes through the third collection tube 24 and the third connection tube and leads to the muscle strength sensor 22. The muscle strength sensor 22 acquires muscle strength data and transmits it to the microprocessor 14. The microprocessor 14 calculates the muscle strength of the user based on the muscle strength data and displays it on the display screen 5.

[0070] In the above embodiment, the pressure difference measurement airway 3 and the muscle strength measurement airway 21 are temporarily assembled during use and are not fixedly arranged in the inner cavity of the housing. Therefore, it is necessary to ensure the fixation of the pressure difference measurement airway 3 or the muscle strength measurement airway 21 in the perforation 29.

[0071] As Figure 5 、 7 shown, shaft shoulders 30 and 31 are coaxially provided on the pressure difference measurement airway 3 and the muscle strength measurement airway 21 respectively. A plurality of (for example, not less than 3) locking jaws 8 are arranged at intervals along the circumferential direction on the outer peripheral surfaces of the shaft shoulders 30 and 31. Fixing grooves can be correspondingly arranged on the inner wall of the perforation 29. After inserting the pressure difference measurement airway 3 or the muscle strength measurement airway 21 into the perforation 29, the locking jaws 8 are correspondingly snapped into the fixing grooves, thereby realizing the fixation of the pressure difference measurement airway 3 or the muscle strength measurement airway 21 in the perforation 29.

[0072] In addition, when assembling the pressure difference measurement airway 3, it is necessary to ensure that the first collection tube 10 and the second collection tube 23 are aligned with the first adapter tube 35 and the second adapter tube 36 on the adapter seat 7, respectively, and to ensure the airtightness of the connection to avoid air leakage and affect the measurement accuracy. Similarly, when assembling the muscle strength measurement airway 21, it is necessary to ensure that the third collection tube 24 is aligned with the third adapter tube 37, and to ensure the tightness of the connection between the third collection tube 24 and the third adapter tube 37 to avoid air leakage and affect the measurement accuracy.

[0073] To this end, in one embodiment of the present application, Figure 1 , 9 As shown, the front end of the handle cover 2 is provided with an adapter column 19 sleeved outside the through hole 29, and the adapter column 19 can be integrally arranged with the handle cover 2 body, and the adapter column 19 is in the shape of a ring coaxially arranged with the through hole 29, and the outer peripheral wall of the front end of the adapter column 19 is provided with a plurality of connecting undercuts 20 (for example, no less than 3 connecting undercuts 20 can be provided) arranged in a circle around its own axial interval, and the connecting undercuts 20 protrude radially outward from the through hole 29, and the outer peripheral surface of the connecting undercut 20 is provided with a buckle 39 recessed radially inwardly. The pulmonary function instrument also includes a decorative fixed rotating cover 4 that can be fastened on the adapter column 19 to position the pressure difference measurement airway 3 or the muscle strength measurement airway 21 in the through hole 29.

[0074] like Figure 1 , 6 As shown in , 8 and 9, the decorative fixed rotating cover 4 is in a circular ring shape and can be coaxially mounted on the adapter column 19. The center of the decorative fixed rotating cover 4 and the center of the adapter column 19 can be passed through by the pressure difference measurement airway 3 or the muscle strength measurement airway 21.

[0075] The rear end surface of the decorative fixed rotating cover 4 is provided with an embedding groove 40 for the adapter column 19 and the connecting undercut 20 thereon to be embedded, and the rear end surface of the decorative fixed rotating cover 4 is provided with a limiting groove 17 corresponding to the connecting undercut 20, and a lock buckle 18 is provided in the limiting groove, and the lock buckle 18 protrudes radially toward the center. The embedding groove 40 is aligned with the adapter column 19 and the connecting undercut 20 thereon, so that the decorative fixed rotating cover 4 is rotated on the adapter column 19, and then the decorative fixed rotating cover 4 is continuously rotated relative to the handle cover 2, so that the connecting undercut 20 is respectively close to the corresponding limiting groove 17, until the clamping head of the lock buckle 18 in the limiting groove 17 is just aligned with the buckle 39 on the connecting undercut 20 in the radial direction and is clamped into the corresponding buckle 39, thereby realizing the fixing of the decorative fixed rotating cover 4 on the handle cover 2.

[0076] likeFigure 1 , 5 As shown in FIGS. 7 to 8, a plurality of airway limiting blocks 16 surrounding a circle are arranged at intervals along the circumferential direction of the inner wall of the decorative fixed rotary cover 4. Correspondingly, a step contact surface 32 is provided on the inner wall at the rear end of the through hole 29.

[0077] After inserting the differential pressure measurement airway 3 or the muscle strength measurement airway 21 into the through hole 29, the decorative fixed rotary cover 4 is sleeved and fixed on the adapter post 19. By screwing the decorative fixed rotary cover 4 onto the handle cover 2, the airway limiting block 16 abuts against the front end surfaces of the shoulders 30, 31, and the rear end surfaces of the shoulders 30, 31 abut against the step contact surface 32, so that the differential pressure measurement airway 3 or the muscle strength measurement airway 21 is fixed between the step contact surface 32 and the airway limiting block 16, realizing the positioning of the differential pressure measurement airway 3 or the muscle strength measurement airway 21 in the through hole 29. At this time, the first collection tube 10 on the differential pressure measurement airway 3 is aligned and hermetically communicated with the first connecting tube 11, and the second collection tube 23 is aligned and hermetically communicated with the second connecting tube 34; or, the third collection tube 24 on the muscle strength measurement airway 21 is aligned and hermetically communicated with the third connecting tube, ensuring the sealing of the airway connection.

[0078] Further, a soft layer 9 is provided on the surface of the adapter base 7 facing the differential pressure measurement air passage 3 and the muscle strength measurement air passage 21. For example, the soft layer 9 can be a silica gel pad. First through holes 25 sleeving on the first adapter tube 35, second through holes 26 sleeving on the second adapter tube 36, and third through holes 27 sleeving on the third adapter tube 37 are respectively formed in the soft layer 9. When the soft layer 9 is in an uncompressed state, the upper end of the first through hole 25 protrudes above the upper end of the first adapter tube 35, the upper end of the second through hole 26 protrudes above the upper end of the second adapter tube 36, and the upper end of the third through hole 27 protrudes above the upper end of the third adapter tube 37. Thus, after the differential pressure measurement air passage 3 or the muscle strength measurement air passage 21 is installed in place in the through hole 29, the first collection tube 10 and the second collection tube 23 will respectively pass through the first through hole 25 and the second through hole 26 and be docked with the first adapter tube 35 and the second adapter tube 36; or, the third collection tube 24 will pass through the third through hole 27 and be aligned and communicated with the third adapter tube 37. Thus, the soft layer 9 is squeezed, so that the first collection tube 10 and the second collection tube 23 on the differential pressure measurement air passage 3 or the third collection tube 24 on the muscle strength measurement air passage 21 are in interference fit with the soft layer 9, and the tighter it is pressed, the better. In this way, it can ensure a tight fit, reduce errors during the assembly and disassembly processes, improve the overall assembly accuracy, effectively solve the installation problem of components, ensure the stability and accuracy of mechanical components during operation, improve the running smoothness of the mechanical equipment, and significantly enhance the sealing effect. The adapter base 7 provides a foundation for installing the soft layer 9 and upward support.

[0079] Guide grooves 41 are provided on the inner wall of the through hole 29 to guide the first collection tube 10 and the second collection tube 23 into the through hole 29 when the differential pressure measurement air passage 3 penetrates into the through hole 29, or to guide the third collection tube 24 into the through hole 29 when the muscle strength measurement air passage 21 penetrates into the through hole 29.

[0080] The pulmonary function instrument can also be provided with a communication module. The microprocessor 14 is communicatively connected to a remote monitoring platform and / or client based on the communication module. The monitoring platform or client can be a personal computer, a laptop computer, a smart phone, a tablet computer, a smart speaker, a smart TV, a smart vehicle device, etc. The smart device has an application program that allows communication with the device and acts as a controller. For example, the communication module can be Bluetooth.

[0081] The automatic detection and calibration system for a pulmonary function meter developed in the embodiments of this application includes a first thin-film piezoelectric sheet respectively disposed on the upper end faces of the first adapter tube 35 and the second adapter tube 36, and a second thin-film piezoelectric sheet disposed on the upper end face of the third adapter tube 37. The first thin-film piezoelectric sheet and the second thin-film piezoelectric sheet can cover or partially cover the upper end faces of the first adapter tube 35, the second adapter tube 36, or the third adapter tube 37. For example, the first thin-film piezoelectric sheet and the second thin-film piezoelectric sheet can be annular.

[0082] Specifically, based on the piezoelectric effect, when the thin-film piezoelectric sheet is subjected to external forces (such as pressure, bending, vibration), the lattice structure inside the material deforms, resulting in the separation of the positive and negative charge centers, and polarization charges (voltage) are generated on the surface. And there is a positive correlation between the voltage generated by the thin-film piezoelectric sheet and the deformation, that is, the greater the deformation, the higher the generated voltage.

[0083] When the differential pressure measurement airway 3 is passed through the housing, if the first collection tube 10 and the second collection tube 23 are respectively docked with the first adapter tube 35 and the second adapter tube 36 in place, the first collection tube 10 and the second collection tube 23 will respectively contact the first thin-film piezoelectric sheets on the upper end faces of the first adapter tube 35 and the second adapter tube 36, and the first thin-film piezoelectric sheets will be deformed under pressure to generate voltage. Similarly, when the muscle strength measurement airway 21 is passed through the housing, if the third collection tube 24 is docked with the third adapter tube 37, the third collection tube 24 will contact the second thin-film piezoelectric sheet on the upper end face of the third adapter tube 37, and the second thin-film piezoelectric sheet will be deformed under pressure to generate voltage.

[0084] In this way, by detecting the magnitudes of the real-time voltages output by the first thin-film piezoelectric sheet and the second thin-film piezoelectric sheet, it is possible to identify whether the differential pressure measurement airway 3 or the muscle strength measurement airway 21 is installed in place.

[0085] In addition, the automatic detection and calibration system further includes a first temperature sensor for detecting the ambient temperature and a second temperature sensor for detecting the temperature of the gas to be detected in the differential pressure sensor 12; wherein, the ambient temperature refers to the atmospheric temperature, and the first temperature sensor can be disposed inside or on the outer wall of the housing, but in order to protect the first temperature sensor, it is preferably disposed inside the housing. Since the housing communicates with the atmosphere, the internal and external ambient temperatures of the housing are the same. Some differential pressure sensors 12 have a built-in temperature detection function. In this case, the second temperature sensor refers to the component in the differential pressure sensor 12 for measuring the temperature of the gas to be detected.

[0086] Further, the automatic detection and calibration system further includes a first detection module for detecting the voltage and current on the battery 13 and the power supply circuit; the battery 13 supplies power to the electrical equipment of the spirometer through the power supply circuit, and the battery 13 and the power supply circuit are the power supply system of the spirometer.

[0087] The automatic detection and calibration system further includes a second detection module for detecting the current and voltage of the electrical equipment such as the communication module, the first thin-film piezoelectric sheet, the second thin-film piezoelectric sheet, the first temperature sensor, and the second temperature sensor respectively;

[0088] The automatic detection and calibration system further includes an alarm and a controller. The signal input end of the controller is respectively connected to the first thin-film piezoelectric sheet, the second thin-film piezoelectric sheet, the first detection module, and the second detection module for receiving corresponding acquisition signals. The signal output end of the controller outputs a control signal, and the control signal is used to control the alarm, the power supply system, and the microprocessor 14 (when the controller is a part of the microprocessor 14, it is to control other modules). When the controller identifies that the spirometer is abnormal based on the acquisition signal, it can send a control signal to the alarm to make it generate an alarm action. The alarm can be a common sound and light alarm, such as a buzzer, an LED alarm light, etc.

[0089] It should be noted that the controller can be a part of the above-mentioned microprocessor 14 or can be set independently of the microprocessor 14.

[0090] Embodiment 2

[0091] Figure 10 It is a schematic flowchart of a method for automatically detecting and calibrating a spirometer in an embodiment of the present invention. The controller in Embodiment 1 can use this method to automatically detect and calibrate the spirometer. As Figure 10 shown, the method includes:

[0092] Step S100, in response to the user's power-on operation of the spirometer, detect whether the installation status of the differential pressure measurement airway 3 or the muscle strength measurement airway 21 on the housing is normal.

[0093] Specifically, before the spirometer is powered on, the user needs to insert the measurement airway 3 or the muscle strength measurement airway 21 into the perforation 29 of the housing according to specific detection requirements, and then press the power switch button on the spirometer to turn it on. After the spirometer is powered on, the controller starts to identify whether the installation status of the measurement airway 3 or the muscle strength measurement airway 21 on the housing is normal. Among them, the normal installation status of the measurement airway 3 on the housing means that the first collection tube 10 and the second collection tube 23 are respectively aligned with and airtightly docked to the first adapter 35 and the second adapter 36; conversely, the abnormal installation status of the measurement airway 3 on the housing means that there is air leakage between the first collection tube 10 and the first adapter 35, and / or there is air leakage between the second collection tube 23 and the second adapter 36. Similarly, the normal installation status of the muscle strength measurement airway 21 on the housing means that the third collection tube 24 is aligned with and airtightly docked to the third adapter 37; conversely, the abnormal installation status of the muscle strength measurement airway 21 on the housing means that there is air leakage between the third collection tube 24 and the third adapter 37.

[0094] Further, the step S100 specifically includes:

[0095] Step S110, respectively obtain the real-time voltages output by the first thin-film piezoelectric sheet and the second thin-film piezoelectric sheet;

[0096] Step S120, based on the real-time voltages, determine whether the installation status of the differential pressure measurement airway 3 or the muscle strength measurement airway 21 on the housing is normal.

[0097] The step S120 specifically includes:

[0098] When the real-time voltages output by the two first thin-film piezoelectric sheets are both within the first preset voltage range, and the real-time voltage output by the second thin-film piezoelectric sheet is zero or close to zero, it is determined that the differential pressure measurement airway 3 is installed and the installation status of the differential pressure measurement airway 3 is normal;

[0099] When the real-time voltage output by at least one of the first thin-film piezoelectric sheets is not within the corresponding first preset voltage range and is not zero, and at the same time the real-time voltage output by the second thin-film piezoelectric sheet is zero, it is determined that the differential pressure measurement airway 3 is installed and the installation status of the differential pressure measurement airway 3 is abnormal;

[0100] When the real-time voltages output by the two second thin-film piezoelectric sheets are both within the second preset voltage range, and the real-time voltage output by the first thin-film piezoelectric sheet is zero, it is determined that the muscle strength measurement airway 21 is installed and the installation status of the muscle strength measurement airway 21 is normal;

[0101] When the real-time voltage output by at least one of the second thin-film piezoelectric wafers is not within the corresponding second preset voltage range and is not zero, and the real-time voltage output by the first thin-film piezoelectric wafer is zero, it is determined that the muscle force measurement airway 21 is installed and the installation state of the muscle force measurement airway 21 is abnormal.

[0102] When the real-time voltage output by the first thin-film piezoelectric wafer is zero and the real-time voltage output by the second thin-film piezoelectric wafer is zero, it is determined that the differential pressure measurement airway 3 and the muscle force measurement airway 21 are not installed.

[0103] Specifically, in the embodiment of the present application, by measuring in advance the minimum voltage and the maximum voltage output by the first thin-film piezoelectric wafer or the second thin-film piezoelectric wafer when the installation state of the differential pressure measurement airway 3 or the muscle force measurement airway 21 on the housing is normal, they are respectively used as the end values of the corresponding preset voltage range. Among them, the preset voltage range corresponding to the first thin-film piezoelectric wafer is the first preset voltage range, and the preset voltage range corresponding to the second thin-film piezoelectric wafer is the second voltage threshold. When the real-time voltage output by the first thin-film piezoelectric wafer falls within the first preset voltage range, it indicates that the installation state of the differential pressure measurement airway 3 is normal. When the real-time voltage output by the second thin-film piezoelectric wafer falls within the second preset voltage range, it indicates that the installation state of the muscle force measurement airway 21 is normal.

[0104] Step S200, when it is detected that the installation state of the differential pressure measurement airway 3 or the muscle force measurement airway 21 is abnormal, an alarm instruction is issued;

[0105] When it is detected that the installation state of the differential pressure measurement airway 3 or the muscle force measurement airway 21 is normal, it is checked whether the power supply state of the power supply system is normal.

[0106] Specifically, the alarm instruction is used to drive the alarm to alarm, so as to remind the user to adjust the differential pressure measurement airway 3 or the muscle force measurement airway 21. After the user shuts down, the differential pressure measurement airway 3 or the muscle force measurement airway 21 can be reinserted, and then the controller restarts to execute step S100.

[0107] When it is detected that the installation state of the differential pressure measurement airway 3 or the muscle force measurement airway 21 is normal, the controller starts to check whether the power supply state of the power supply system of the pulmonary function instrument is normal.

[0108] The first detection module detects the first voltage and the first current output by the battery 13 in real time and transmits them to the controller. The third preset voltage range and the first preset current range are pre-stored in the controller. The controller compares the first voltage with the third preset voltage range, and the first current with the first preset current range. When the first voltage is within the third preset voltage range and the first current is within the first preset current range, it is determined that the battery 13 is supplying power normally; when the first voltage is not within the third preset voltage range and / or the first current is not within the first preset current range, it is determined that the battery 13 is supplying power abnormally.

[0109] The first detection module also detects the second voltage and the second current on the power supply circuit in real time and transmits them to the controller. The fourth preset voltage range and the second preset current range are pre-stored in the controller. The controller compares the second voltage with the fourth preset voltage range, and the second current with the second preset current range. When the second voltage is within the fourth preset voltage range and the second current is within the second preset current range, it is determined that the battery 13 is supplying power normally. When the second voltage is not within the fourth preset voltage range and / or the second current is not within the second preset current range, it is determined that the power supply circuit is supplying power abnormally.

[0110] When the battery 13 is supplying power abnormally and / or the power supply circuit is supplying power abnormally, it is determined that the power supply system is supplying power abnormally.

[0111] Among them, the above-mentioned third preset voltage range, the first preset current range, the fourth preset voltage range, and the second preset current range can be obtained by pre-calculation or measurement in advance.

[0112] Step S300, when it is detected that the power supply system is supplying power abnormally, cut off the power supply system and issue an alarm command;

[0113] When it is detected that the power supply system is supplying power normally, detect whether the power-on state of the electrical equipment of the spirometer is normal;

[0114] Specifically, the power supply system includes the above-mentioned battery 13 and the power supply circuit. When it is detected that the power supply system is supplying power abnormally, the controller cuts off the current of the power supply system to avoid causing damage to the lung function. At the same time, an alarm signal is sent to the alarm, and the alarm acts to remind the user.

[0115] After it is detected that the power supply system is supplying power normally, detect whether the power-on states of the electrical equipment of the spirometer are normal respectively.

[0116] Specifically, in the embodiments of the present application, the electrical equipment includes a differential pressure sensor 12, a muscle force sensor 22, a first thin-film piezoelectric sheet, a second thin-film piezoelectric sheet, a first temperature sensor, a second temperature sensor, etc. It judges whether it is abnormal by obtaining whether the current and voltage on it are within the corresponding preset ranges respectively.

[0117] For example, the second detection module detects the third voltage and the third current on the differential pressure sensor 12 in real time and transmits them to the controller. The fifth preset voltage range and the third preset current range are pre-stored in the controller. The controller compares the third voltage with the fifth preset voltage range, and the third current with the third preset current range; when the third voltage is within the fifth preset voltage range and the third current is within the third preset current range, it is judged that the battery 13 is powered on normally; when the third voltage is not within the fifth preset voltage range and / or the third current is not within the third preset current range, it is judged that the differential pressure sensor is powered on abnormally. The judgment of whether the power-on state of other electrical equipment is normal is similar and will not be elaborated here.

[0118] Among them, the above-mentioned fifth preset voltage range and third preset current range can be obtained by pre-calculation or measurement in advance.

[0119] Step S400, when it is detected that any one of the electrical equipment is powered on abnormally, an alarm instruction is issued;

[0120] When it is detected that all electrical equipment is powered on normally, the automatic detection is ended and the automatic calibration process is started.

[0121] Specifically, when any one of the electrical equipment is powered on abnormally, the controller sends an alarm signal to the alarm, and the alarm acts to remind the user.

[0122] Further, the automatic calibration process specifically includes:

[0123] Step S410, obtain the ambient temperature T 0 ;

[0124] Specifically, the ambient temperature T 0 refers to the temperature in the environment where the pulmonary function instrument is used. The first temperature sensor obtains the ambient temperature T 0 , and transmits it to the controller.

[0125] Step S420, obtain the gas temperature T of the gas to be measured inside the differential pressure sensor 1 ;

[0126] Specifically, the second temperature sensor obtains the gas temperature T of the gas to be measured inside the differential pressure sensor 1 , and transmits it to the controller. Among them, the gas to be measured refers to the gas used for measuring the expiratory pressure difference or the inspiratory pressure difference.

[0127] Step S430, when T 0 ≠T 1 , perform temperature compensation on the expiratory pressure difference and / or inspiratory pressure difference detected by the pulmonary function instrument.

[0128] Specifically, gases have different expansion coefficients at different temperatures, and the measurement of expiratory pressure difference or inspiratory pressure difference by a pulmonary function instrument is greatly affected by temperature. The controller obtains the ambient temperature T 0 and the gas temperature T 1 , and after comparing the ambient temperature T 0 and the gas temperature T 1 , when T 0 ≠T 1 , that is, the ambient temperature T 0 is different from the temperature of the gas to be measured inside the differential pressure sensor.

[0129] The embodiment of the present application performs temperature compensation on the expiratory pressure difference and / or inspiratory pressure difference based on the temperature drift curve, that is: ΔP = f(T 0 ) - f(T 1 ), where ΔP is the differential pressure compensation amount of the expiratory pressure difference / or inspiratory pressure difference, and f(x) is the temperature drift curve. Therefore, to improve the accuracy of the measurement results of the pulmonary function instrument, the controller in the embodiment of the present application senses the environmental changes in real time and makes corresponding adjustments to the measurement results, making the measurement results comparable and facilitating doctors' diagnosis and treatment.

[0130] Embodiment 3

[0131] Based on the same inventive concept as a method for automatic detection and calibration of a pulmonary function instrument in the foregoing embodiments, the present invention further provides an automatic detection and calibration device for a pulmonary function instrument, as shown in Figure 11 . The device includes:

[0132] A first detection module 201, configured to detect whether the installation state of the differential pressure measurement airway 3 or the muscle strength measurement airway 21 on the housing is normal in response to a user's operation of turning on the pulmonary function instrument;

[0133] A second detection module 202, configured to issue an alarm instruction when it is detected that the installation state of the differential pressure measurement airway 3 or the muscle strength measurement airway 21 is abnormal; when it is detected that the installation state of the differential pressure measurement airway 3 or the muscle strength measurement airway 21 is normal, obtain whether the power supply state of the power supply system of the pulmonary function instrument is normal;

[0134] A third detection module 203, configured to cut off the power supply system and issue an alarm instruction when it is detected that the power supply of the power supply system is abnormal; when it is detected that the power supply of the power supply system is normal, detect whether the power-on state of the electrical equipment of the pulmonary function instrument is normal;

[0135] The fourth detection module 204 is configured to issue an alarm instruction when any power-on abnormality of the electrical equipment is detected; when it is detected that all the electrical equipment is powered on normally, the automatic detection and calibration is ended, and the automatic calibration process is started.

[0136] Further, the first detection module specifically includes:

[0137] The first acquisition unit is configured to respectively acquire the real-time voltages output by the first thin-film piezoelectric sheet and the second thin-film piezoelectric sheet;

[0138] The first judgment unit is configured to judge whether the installation states of the differential pressure measurement air passage 3 or the muscle force measurement air passage 21 on the housing are normal based on the real-time voltages.

[0139] Furthermore, the fourth detection module includes:

[0140] The second acquisition unit is configured to acquire the ambient temperature T 0 ;

[0141] The third acquisition unit is configured to acquire the gas temperature T of the gas to be measured in the differential pressure sensor 1 ;

[0142] The compensation unit is configured to perform temperature compensation on the expiratory pressure difference and / or inspiratory pressure difference detected by the spirometer when T 0 ≠T 1 .

[0143] Embodiment 4

[0144] Based on the same inventive concept as the method for automatically detecting and calibrating a spirometer in the foregoing embodiments, the present invention further provides an apparatus for automatically detecting and calibrating a spirometer, on which a computer program is stored, and when the program is executed by a processor, the steps of any one of the methods for automatically detecting and calibrating a spirometer described above are implemented.

[0145] Wherein, in Figure 4 , the bus architecture (represented by bus 300), the bus 300 may include any number of interconnected buses and bridges, and the bus 300 links various circuits including one or more processors represented by processor 302 and a memory represented by memory 304 together. The bus 300 may also link various other circuits such as peripheral devices, voltage regulators, and power management circuits, which are well known in the art, and therefore, they will not be further described herein. The bus interface 306 provides an interface between the bus 300 and the receiver 301 and the transmitter 303. The receiver 301 and the transmitter 303 may be the same element, i.e., a transceiver, which provides a unit for communicating with various other devices on the transmission medium.

[0146] The processor 302 is responsible for managing the bus 300 and general processing, while the memory 304 can be used to store data used by the processor 302 during operation.

[0147] Embodiment 5

[0148] Based on the same inventive concept as an automatic detection and calibration method for a pulmonary function instrument in the foregoing embodiments, the present invention also provides a computer-readable storage medium, on which a computer program is stored, and when the program is executed by a processor, each step in Embodiment 2 is implemented.

Claims

1. A pulmonary function meter automatic detection and calibration system, characterized in that: The pulmonary function instrument comprises a shell, wherein a first measuring airway and a second measuring airway are arranged in the shell, wherein the first measuring airway is connected to a pressure difference sensor, and the second measuring airway is connected to a muscle force sensor; The housing can be penetrated by a pressure difference measuring airway or a muscle strength measuring airway, the pressure difference measuring airway is provided with a pressure difference collecting tube, and the muscle strength measuring airway is provided with a muscle strength collecting tube; When the pressure difference measuring airway is arranged in the shell, the pressure difference collecting tube is communicated with the first measuring airway to measure the expiratory pressure difference and / or the inspiratory pressure difference; when the muscle strength measuring airway is arranged in the shell, the muscle strength collecting tube is communicated with the second measuring airway to measure the muscle strength; Also included is a power supply system for supplying power.

2. The automatic detection and calibration system for a pulmonary function meter as claimed in claim 1, characterized in that: The system comprises a first thin film piezoelectric sheet disposed on the first measuring gas channel and a second thin film piezoelectric sheet disposed on the second measuring gas channel; When the differential pressure measuring airway is arranged in the housing, the differential pressure collecting tube is connected to the first measuring airway and contacts the first thin film piezoelectric sheet; When the muscle force measurement airway is inserted into the housing, the muscle force collection tube is docked with the second measurement airway and contacts the second thin film piezoelectric sheet.

3. The automatic detection and calibration system for a pulmonary function meter as claimed in claim 2, characterized in that: The system further comprises a first temperature sensor for detecting the ambient temperature and a second temperature sensor for detecting the temperature of the gas to be detected in the differential pressure sensor; The system also includes an alarm and a controller. The signal input end of the controller is connected to the first thin film piezoelectric sheet, the second thin film piezoelectric sheet, the first temperature sensor, and the second temperature sensor, respectively, and is used to receive signals. The signal output end of the controller outputs a control signal, and the control signal is used to control the alarm and the pulmonary function meter.

4. A method for automatic detection and calibration of a pulmonary function instrument, characterized in that: The method comprises: In response to the user's power-on operation on the pulmonary function instrument, detecting whether the installation state of the pressure difference measurement airway or the muscle strength measurement airway on the housing is normal; When it is detected that the installation state of the pressure difference measuring airway or the muscle strength measuring airway is abnormal, an alarm instruction is issued; when it is detected that the installation state of the pressure difference measuring airway or the muscle strength measuring airway is normal, whether the power supply state of the power supply system of the pulmonary function instrument is normal; When it is detected that the power supply of the power supply system is abnormal, the power supply system is cut off and an alarm instruction is issued; when it is detected that the power supply of the power supply system is normal, the power supply status of the electrical equipment of the pulmonary function instrument is normal; When it is detected that any electrical device is powered on abnormally, an alarm command is issued; when it is detected that all electrical devices are powered on normally, the automatic detection and calibration is ended, and the automatic calibration process is started.

5. A method for automatic detection and calibration of a pulmonary function meter as claimed in claim 4, characterized in that: The step of detecting whether the installation state of the pressure difference measurement airway or the muscle strength measurement airway on the housing is normal specifically includes: Respectively obtain the real-time voltage output by the first thin film piezoelectric sheet and the second thin film piezoelectric sheet; Based on the real-time voltage, it is determined whether the installation state of the pressure difference measurement airway or the muscle strength measurement airway on the housing is normal.

6. A method for automatic detection and calibration of a pulmonary function meter as claimed in claim 4, characterized in that: The automatic calibration process includes: Get the ambient temperature T0; Acquiring the gas temperature T1 of the gas to be measured in the differential pressure sensor; When T0≠T1, temperature compensation is performed on the expiratory pressure difference and / or the inspiratory pressure difference detected by the pulmonary function instrument.

7. A method for automatic detection and calibration of a pulmonary function meter as claimed in claim 6, characterized in that: The temperature compensation of the expiratory pressure difference and / or the inspiratory pressure difference detected by the pulmonary function instrument specifically includes: The expiratory pressure difference and / or inspiratory pressure difference is temperature compensated based on the temperature drift curve, that is: ΔP=f(Τ0)-f(Τ1), wherein ΔP is the compensation amount of the expiratory pressure difference and / or inspiratory pressure difference, and f(x) is the temperature drift curve.

8. An automatic detection and calibration device for a pulmonary function meter, characterized in that: The device comprises: A first detection module is used to detect whether the installation state of the pressure difference measurement airway or the muscle strength measurement airway on the housing is normal in response to the user's power-on operation of the pulmonary function instrument; The second detection module is used to issue an alarm instruction when it is detected that the installation state of the pressure difference measurement airway or the muscle strength measurement airway is abnormal; when it is detected that the installation state of the pressure difference measurement airway or the muscle strength measurement airway is normal, obtain whether the power supply state of the power supply system of the pulmonary function instrument is normal; The third detection module is used to cut off the power supply system and issue an alarm command when it is detected that the power supply of the power supply system is abnormal; when it is detected that the power supply of the power supply system is normal, detect whether the power-on state of the electrical equipment of the pulmonary function instrument is normal; The fourth detection module is used to issue an alarm instruction when it detects that any electrical device is powered on abnormally; when it is detected that all electrical devices are powered on normally, end the automatic detection and calibration, and start the automatic calibration process.

9. An automatic detection and calibration device for a pulmonary function meter, comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, characterized in that: When the processor executes the program, the method according to any one of claims 4 to 7 is implemented.

10. A computer-readable storage medium having a computer program stored thereon, characterized in that: When the program is executed by a processor, the method according to any one of claims 4 to 7 is implemented.

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