A respiratory monitoring device and method of operation thereof

Abstract

This invention discloses a respiratory monitoring device and its working method, relating to the field of pulmonary function monitoring technology. The respiratory monitoring device includes a flexible chest strap and a flexible shoulder strap. One end of the flexible shoulder strap is sewn to the flexible chest strap. A chest rise and fall acquisition mechanism is installed on one side of the front end of the flexible chest strap, and a lung sound acquisition mechanism is installed on the other side of the front end of the flexible chest strap. A control box is installed on the outer wall of the flexible shoulder strap, and a wire is installed at the upper end of the control box. A respiratory sound acquisition mechanism is installed at one end of the wire. This solution solves the problems of existing pulmonary function monitoring devices being unable to perform real-time monitoring, only being able to monitor pulmonary function through inhaled and exhaled gases, having a single measurement parameter, and low accuracy.

Description

Technical Field

[0001] This invention relates to the field of lung function monitoring technology, specifically to a respiratory monitoring device and its working method. Background Technology

[0002] Patients diagnosed with asthma, chronic obstructive pulmonary disease, etc., often need to rely on pulmonary function monitors to measure the volume of air inhaled and exhaled from the lungs during follow-up visits or health management, as well as patients who have undergone lung surgery or lung transplantation and are performing lung breathing exercises. This allows for pulmonary function testing and tracking of lung health.

[0003] Current lung function monitoring devices, such as the turbine-type lung function monitor mentioned in announcement number CN220193012U, include a top cover, a shell, an air inlet tube, and an adjustment tube. The top of the top cover is provided with a first assembly tube, and the top of the shell is provided with a second assembly tube. The second assembly tube is provided with a first turbine fan inside. One end of the air inlet tube is inserted into the interior of the first assembly tube, and one end of the adjustment tube is inserted into the interior of the second assembly tube. A through air outlet is opened on the outer surface of the middle part of the adjustment tube. A rotating ring is fitted on the outer surface of the other end of the adjustment tube. One end of the rotating ring has an array of adjustment holes with progressively decreasing areas on its outer surface. A cover plate is provided on the end of the adjustment tube near the rotating ring.

[0004] However, existing lung function monitoring devices cannot perform real-time monitoring and can only monitor lung function through inhaled and exhaled gases. The measurement parameters are limited and the accuracy is low. Therefore, we provide a respiratory monitoring device and its working method. Summary of the Invention

[0005] The purpose of this invention is to provide a respiratory monitoring device and its working method to solve the problems mentioned in the background art, such as the inability of existing lung function monitoring devices to perform real-time monitoring, the inability to monitor lung function only through inhaled and exhaled gases, the limited measurement parameters, and the low accuracy.

[0006] To achieve the above objectives, the present invention provides the following technical solution: a respiratory monitoring device, comprising a flexible chest strap and a flexible shoulder strap, one end of the flexible shoulder strap being sewn together with the flexible chest strap, a chest rise and fall acquisition mechanism being installed on one side of the front end of the flexible chest strap, a lung sound acquisition mechanism being installed on the other side of the front end of the flexible chest strap, a control box being installed on the outer wall of the flexible shoulder strap, a wire being installed at the upper end of the control box, and a respiratory sound acquisition mechanism being installed at one end of the wire.

[0007] Preferably, the chest wall movement acquisition mechanism includes a first positioning plate, a lower housing, and an upper housing. The first positioning plate is disposed on the outer wall of the flexible chest band, the lower housing is disposed on the inner wall of the flexible chest band, and the four corners of the first positioning plate are connected to the lower housing by screws. The upper housing is disposed above the lower housing, and the four corners of the lower housing are connected to the upper housing by springs. The upper surface of the lower housing is provided with a cross-shaped pressure groove. A pressure transmission column is installed at the middle position of the lower end of the upper housing. Flexible thin-film pressure sensors are disposed around the outer wall of the pressure transmission column, and the flexible thin-film pressure sensors are distributed in a cross shape. A fitting cover is provided at the upper end of the upper housing.

[0008] Preferably, a transmission column limiting groove is provided at the middle position inside the cross-shaped pressure groove, and a limiting column is provided on the inner side of the spring.

[0009] Preferably, the lung sound acquisition mechanism includes a second positioning plate, a base, and a heart sound sensor. The second positioning plate is disposed on the outer wall of the flexible chest band, the base is disposed on the inner wall of the flexible chest band, and the four corners of the second positioning plate are connected to the base by screws. The heart sound sensor is disposed at the lower end of the base.

[0010] Preferably, the breathing sound acquisition mechanism includes a terminal block, a rotating arm support, a first rotating arm, a second rotating arm, a collector, and a horn-shaped microphone. The rotating arm support is installed on the outer wall of the terminal block, the first rotating arm is installed at one end of the terminal block, the second rotating arm is installed at one end of the first rotating arm, the collector is installed at one end of the second rotating arm, and the horn-shaped microphone is installed at one end of the collector.

[0011] Preferably, the rotating arm support, the first rotating arm, the second rotating arm, and the data collector are rotatably connected by a damping shaft.

[0012] Preferably, the terminal block is provided with strap buckles on both sides, and the strap buckles on both sides are inclined inward.

[0013] Preferably, one end of the flexible chest strap is fitted with a fold-over fold, and the other end of the flexible chest strap is fitted with Velcro, which penetrates and extends into the interior of the fold-over fold and is bonded to the flexible chest strap. A fastening buckle is fitted on the outer wall of the other end of the flexible shoulder strap, and a connecting strap is fitted on the outer wall of the fastening buckle, with one end of the connecting strap sewn to the inner wall of the flexible chest strap.

[0014] Preferably, the control box is internally equipped with an AD conversion module, a main control module, a power supply module, a WIFI module, and an FPGA code module.

[0015] Preferably, the method of using a respiratory monitoring device and its operating method includes the following steps:

[0016] Step 1: The person to be monitored first wears the chest rise and fall acquisition mechanism and lung sound acquisition mechanism on the chest through the flexible chest strap and flexible shoulder strap. Then, the person wears the device on the head using the elastic straps on the two sides of the respiratory sound acquisition mechanism. By rotating the first and second rotating arms, the horn-shaped microphone is rotated to the mouth, thus completing the wearing of the device.

[0017] Step 2: Start the device. The device collects the intensity of breath sounds through a horn-shaped microphone placed at the mouth, collects the changes in chest rise and fall through a flexible thin-film pressure sensor placed on the chest, and collects lung sounds through a heart sound sensor placed on the front of the lungs. This obtains three physiological signals from different parts of the human body. Each signal is converted into a digital signal by an AD conversion module after passing through the corresponding conditioning circuit.

[0018] Step 3: The FPGA code module controls the three AD chips in parallel to read, integrate, and classify the data;

[0019] Step 4: After integration, the FPGA code module further processes the data across clock cycles, packages it, and sends it to the host computer software via the WIFI module through the control data flow.

[0020] Step 5: The host computer unpacks and classifies the data, restores the data according to the corresponding data calculation method, and displays and analyzes the data.

[0021] Compared with the prior art, the beneficial effects of the present invention are:

[0022] This invention measures respiratory disturbances through multi-parameter monitoring, resulting in greater accuracy. It also features a self-designed mechanical structure suitable for chest pressure and breath sound measurements, improving accuracy and response speed. Furthermore, the entire device utilizes flexible, stretchable materials and is designed as a wearable device, allowing for more precise measurement point settings over extended periods. Prolonged use does not significantly impact the user's physiology. This invention addresses the limitations of existing lung function monitoring devices, which lack real-time monitoring capabilities, rely solely on inhaled and exhaled air for lung function monitoring, and suffer from limited measurement parameters and low accuracy. Attached Figure Description

[0023] Figure 1 This is a schematic diagram of the overall structure of the present invention;

[0024] Figure 2 This is a schematic diagram of the rear structure of the present invention;

[0025] Figure 3 This is a schematic diagram of the overall structure of the chest wall rise and fall acquisition mechanism of the present invention;

[0026] Figure 4This is a front structural diagram of the chest wall undulation acquisition mechanism of the present invention;

[0027] Figure 5 This is a schematic diagram of the overall structure of the respiratory sound acquisition mechanism of the present invention;

[0028] Figure 6 This is a schematic diagram of the thoracic pressure acquisition circuit of the present invention;

[0029] Figure 7 This is a circuit diagram of the heart sound sensor of the present invention;

[0030] Figure 8 This is a schematic diagram of the lung sound acquisition circuit of the present invention;

[0031] Figure 9 This is a schematic diagram of the breathing sound acquisition circuit of the present invention;

[0032] Figure 10 This is a diagram of the internal structure of the AD9280 of the present invention;

[0033] Figure 11 This is the FPGA schematic diagram of the present invention;

[0034] Figure 12 This is a block diagram of the FPGA code design for the present invention;

[0035] In the diagram: 1. Flexible chest strap; 2. Fold-down clasp; 3. Velcro; 4. Flexible shoulder strap; 5. Fastening buckle; 6. Connecting strap; 7. Chest movement acquisition mechanism; 701. First positioning plate; 702. Lower housing; 703. Pressure transmission column; 704. Spring; 705. Upper housing; 706. Limiting column; 707. Flexible thin-film pressure sensor; 708. Cross-shaped pressure groove; 709. Fitting cover; 710. Transmission column limiting groove; 8. Lung sound acquisition mechanism; 801. Second positioning plate; 802. Base; 803. Heart sound sensor; 9. Control box; 10. Wire; 11. Breath sound acquisition mechanism; 111. Terminal block; 112. Strap connecting buckle; 113. Rotating arm support; 114. First rotating arm; 115. Second rotating arm; 116. Acquisition device; 117. Horn-shaped microphone; 118. Damping shaft. Detailed Implementation

[0036] The technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments.

[0037] Please see Figure 1-12An embodiment of the present invention provides a respiratory monitoring device, comprising a flexible chest strap 1 and a flexible shoulder strap 4. One end of the flexible shoulder strap 4 is sewn to the flexible chest strap 1. A chest rise and fall acquisition mechanism 7 is installed on one side of the front end of the flexible chest strap 1, and a lung sound acquisition mechanism 8 is installed on the other side of the front end of the flexible chest strap 1. A control box 9 is installed on the outer wall of the flexible shoulder strap 4. A wire 10 is installed on the upper end of the control box 9, and a respiratory sound acquisition mechanism 11 is installed on one end of the wire 10.

[0038] Please see Figure 3 The chest rise and fall acquisition mechanism 7 includes a first positioning plate 701, a lower housing 702, and an upper housing 705. The first positioning plate 701 is disposed on the outer wall of the flexible chest band 1, and the lower housing 702 is disposed on the inner wall of the flexible chest band 1. The four corners of the first positioning plate 701 are connected to the lower housing 702 by screws. The upper housing 705 is disposed above the lower housing 702. The four corners of the lower housing 702 are connected to the upper housing 705 by springs 704. The upper surface of the lower housing 702 is provided with a cross-shaped pressure groove 708. A pressure transmission column 703 is installed at the middle position of the lower end of the upper housing 705. Flexible thin film pressure sensors 707 are provided around the outer wall of the pressure transmission column 703, and the flexible thin film pressure sensors 707 are distributed in a cross shape. The upper end of the upper housing 705 is provided with a fitting cover 709. A transmission column limiting groove 710 is provided at the middle position inside the cross-shaped pressure groove 708. A limiting column 706 is provided on the inner side of the spring 704.

[0039] Since the chest cavity rises and falls in a reciprocating motion, the change in force applied to the surface of the flexible thin-film pressure sensor 707 during this motion is converted into a change in the sensor's resistance, and then this change in resistance is converted into a change in voltage. Figure 1 and Figure 3 As shown, the flexible chest strap 1 is worn on the chest. The back-and-forth movement of the rib cage during breathing drives the upper housing 705 to move, causing the flexible thin film pressure sensor 707 to be pressed into the cross-shaped pressure groove 708. The springs 704 installed at the four corners are responsible for springing the upper housing 705 back when the rib cage retracts. This design makes the resistance of the pressure sensor increase and decrease respectively when the rib cage expands inside and outside.

[0040] The flexible thin-film pressure sensor 707 is composed of a polyester film with excellent comprehensive mechanical properties, highly conductive materials, and nano-scale pressure-sensitive materials. The top layer is a flexible thin film and a pressure-sensitive layer laminated on it, while the bottom layer is a flexible thin film and conductive lines laminated on it. The two are bonded together with double-sided adhesive and the sensing area is isolated. When the sensing area is compressed, the disconnected lines on the bottom layer will be connected through the pressure-sensitive layer on the top layer, so that the resistance output value of the port changes with the pressure, thereby realizing pressure detection.

[0041] Since the pressure sensor has converted the pressure into a change in resistance, a series resistor sampling method is used to convert it into a voltage value. Due to the influence of mechanical force during the sampling process of the pressure sensor, a voltage follower circuit needs to be added before the collected voltage is sent to the AD converter to isolate the front and rear stages, reduce interference between the front and rear stages, and improve the acquisition quality. The voltage follower circuit is composed of a low-noise LM358 operational amplifier, and the last stage uses a variable resistor to adjust the voltage value.

[0042] Under no pressure, the maximum resistance is 10K. This can be converted by connecting a 10k resistor in series. The conversion formula is:

[0043]

[0044] V O For voltage conversion, R S R is the resistance of the pressure sensor, and R is the series resistance. Its circuit diagram is shown below. Figure 6 As shown.

[0045] Furthermore, the lung sound acquisition mechanism 8 includes a second positioning plate 801, a base 802, and a heart sound sensor 803. The second positioning plate 801 is disposed on the outer wall of the flexible chest band 1, the base 802 is disposed on the inner wall of the flexible chest band 1, and the four corners of the second positioning plate 801 are connected to the base 802 by screws. The heart sound sensor 803 is disposed at the lower end of the base 802.

[0046] Because lung sounds are weak, the HDY-06E heart sound sensor 803 is used for acquisition. The heart sound sensor 803 uses a capacitive micro-phonic sensing element to acquire heartbeat and other superficial arterial pulsation signals, which are then processed by a highly integrated signal circuit to output a low-impedance audio voltage signal, such as... Figure 7 The diagram shown is a schematic of its internal circuit.

[0047] Since the voltage output range of the heart sound sensor 803 is -2.5V to +2.5V, and the input signal range of the AD chip is 0V to 2V, a difference circuit composed of a low-noise operational amplifier is used to proportionally shift the signal to a positive signal within the range of 0V to 2V. Figure 8 As shown, the reference voltage provided by the AD chip is attenuated to -1V by an inverting amplifier and then fed into the N terminal of the difference circuit. The output voltage of the lung sound sensor is fed into the P terminal of the difference circuit through a variable resistor. The calculation formula is as follows:

[0048] U O =2U S +1

[0049] U o For the final conversion voltage, U s This is the output voltage of the pressure sensor.

[0050] Please see Figure 5 The breathing sound acquisition mechanism 11 includes a terminal block 111, a rotating arm support 113, a first rotating arm 114, a second rotating arm 115, a collector 116, and a horn-shaped microphone 117. The rotating arm support 113 is installed on the outer wall of the terminal block 111. The first rotating arm 114 is installed at one end of the terminal block 111. The second rotating arm 115 is installed at one end of the first rotating arm 114. The collector 116 is installed at one end of the second rotating arm 115. The horn-shaped microphone 117 is installed at one end of the collector 116. The rotating arm support 113, the first rotating arm 114, the second rotating arm 115, and the collector 116 are rotatably connected by a damping shaft 118. Both sides of the terminal block 111 are provided with strap connecting buckles 112, and the strap connecting buckles 112 on both sides are inclined inward.

[0051] The frequency range of human voices is mainly concentrated in the range of 20Hz-20kHz. Therefore, the collected sound signal only needs to extract the low-frequency components (20Hz-5000Hz). An electret microphone is used to convert the sound signal into an electrical signal. Since the amplitude after conversion is in the millivolt range, the sound signal needs to be amplified by 50 times by a remote amplifier and then filtered by a second-order low-pass filter.

[0052] like Figure 9 As shown, with the filter cutoff frequency set to 500Hz, the formula for calculating the upper cutoff frequency of a second-order filter is:

[0053]

[0054] The calculated values ​​are R = 120 kΩ and C = 1 nF. At this point, f... h ≈496Hz.

[0055] Furthermore, a fold 2 is installed at one end of the flexible breast strap 1, and a Velcro 3 is installed at the other end of the flexible breast strap 1. The Velcro 3 penetrates and extends into the interior of the fold 2 and is bonded to the flexible breast strap 1. A fastening buckle 5 is installed on the outer wall of the other end of the flexible shoulder strap 4, and a connecting strap 6 is installed on the outer wall of the fastening buckle 5. One end of the connecting strap 6 is sewn to the inner wall of the flexible breast strap 1.

[0056] Furthermore, the control box 9 is internally equipped with an AD conversion module, a main control module, a power supply module, a WIFI module, and an FPGA code module;

[0057] Since the three signals are sampled at similar frequency ranges and their amplitudes are all within 0 to 2V after conversion, the AD9280 chip is used. The AD9280 is a monolithic, single-supply, 8-bit, 32MSPS analog-to-digital converter with an on-chip sample-and-hold amplifier and voltage reference. This AD conversion module adopts a multi-stage differential pipeline architecture, has a data rate of 32MSPS, and ensures that no code is lost over the entire operating temperature range.

[0058] like Figure 10 The diagram shown is the schematic of AD9280. After configuring its external mode, all three signals are acquired at a sampling rate of 3kHz. At the same time, since some operational amplifier circuits require a reference voltage, AD9280 also provides a 2V output reference voltage. When taking this reference voltage, it must first pass through a voltage follower circuit for signal isolation.

[0059] Figure 11 The schematic diagram of the main control and power supply section shows that the FPGA used in the main control section is the EP4CE10E22C8 chip. This chip has many logic units and abundant on-chip resources. The clock frequency is 50MHz. The chip mainly includes a power supply section, FLASH, crystal oscillator, reserved I / O ports, as well as switches and LEDs. The power supply section mainly provides 5V, 3.3V, and 2.5V to power the FPGA chip. To ensure the stability of the FPGA during operation, filter capacitors are added to the power supply ports for filtering. The FLASH is used as the memory for writing programs. The crystal oscillator provides an external 50MHz operating clock for the FPGA. The chip uses JTAG program writing method for program writing and debugging.

[0060] The power supply section uses both USB and battery power. When USB is connected, the battery is charged. At this time, the DC-DC section is powered entirely by USB, converting 5V to 3.3V, 2.5V, and -5V to power each module. When USB is not connected, the battery is connected to the circuit for power supply.

[0061] The WIFI module serves as the information interaction module between the host computer and the slave computer. The WIFI module model is ESP8266-01. This module supports the IEEE 802.11b / g / n standard, operates in the 2.4GHz frequency band, and provides a reliable wireless connection. The module has 512KB Flash storage and 80KB RAM built-in, and supports communication with other microcontrollers through the UART interface. The host computer is configured in master mode, and the slave computer is configured in slave mode. The configuration data is configured by the host computer and the slave computer respectively through AT commands during power-on initialization. The bit rate used in this design is 460800.

[0062] like Figure 12The diagram shown is an FPGA code block diagram. The code is mainly divided into three modules: a driver module, a data synthesis module, and an instruction receiving and processing module. The device operates by automatically configuring upon power-on, and then sending instruction signals from the host computer to the slave computer to control the data acquisition switch. The specific workflow is as follows:

[0063] When the device is powered on, the lower-level machine automatically configures the WIFI module and initializes the AD chip. The upper-level machine opens the serial port channel, configures the main WIFI module, and then begins to search for and connect to the WIFI module signal.

[0064] Once the WIFI module is successfully connected, both the host computer and the slave computer will send a flag signal.

[0065] At this time, the host computer presses the start measurement button, and the lower computer instruction receiving and processing module receives the data. According to the instruction type, it will send the corresponding instruction signal to the data integration module and the driver module. At this time, the data integration module will clear the FIFO buffer to prepare to store the data, and the driver module will give the AD signal to start the measurement.

[0066] After the measurement begins, the data from the three channels will be stored in the corresponding FIFOs. The data integration module will determine the amount of data through the flag signal of the FIFO and control the data to be packaged and sent to the sending module at certain time intervals and in a certain format.

[0067] The host computer receives, unpacks, classifies, and calculates the data, and then displays it visually.

[0068] The stop command is similar to the above. The instruction receiving module mainly distinguishes different instruction signals sent by the host computer and issues control signals for different modules.

[0069] Furthermore, the method of using a respiratory monitoring device and its operating method includes the following steps:

[0070] Step 1: The person to be monitored first wears the chest rise and fall acquisition mechanism 7 and lung sound acquisition mechanism 8 on the chest through the flexible chest strap 1 and flexible shoulder strap 4. Then, the person wears the device on the head using the elastic straps on the two side straps connecting buckles 112 of the breath sound acquisition mechanism 11. By rotating the first rotating arm 114 and the second rotating arm 115, the speaker-shaped microphone 117 is rotated to the mouth, thus completing the wearing of the device.

[0071] Step 2: Start the device. The device collects the intensity of breath sounds through the horn-shaped microphone 117 placed at the mouth, collects the changes in chest rise and fall through the flexible thin-film pressure sensor 707 placed on the chest, and collects lung sounds through the heart sound sensor 803 placed on the front of the lungs. This obtains three physiological signals from different parts of the human body. Each signal is converted into a digital signal by an AD conversion module after passing through the corresponding conditioning circuit.

[0072] Step 3: The FPGA code module controls the three AD chips in parallel to read, integrate, and classify the data;

[0073] Step 4: After integration, the FPGA code module further processes the data across clock cycles, packages it, and sends it to the host computer software via the WIFI module through the control data flow.

[0074] Step 5: The host computer unpacks and classifies the data, restores the data according to the corresponding data calculation method, and displays and analyzes the data.

[0075] It will be apparent to those skilled in the art that the present invention is not limited to the details of the exemplary embodiments described above, and that the invention can be implemented in other specific forms without departing from its spirit or essential characteristics. Therefore, the embodiments should be considered in all respects as exemplary and non-limiting, and the scope of the invention is defined by the appended claims rather than the foregoing description. Thus, all variations falling within the meaning and scope of equivalents of the claims are intended to be included within the present invention. No reference numerals in the claims should be construed as limiting the scope of the claims.

Claims

1. A respiratory monitoring device, comprising a flexible chest strap (1) and a flexible shoulder strap (4), characterized in that: One end of the flexible shoulder strap (4) is sewn to the flexible chest strap (1). A chest rise and fall acquisition mechanism (7) is installed on one side of the front end of the flexible chest strap (1), and a lung sound acquisition mechanism (8) is installed on the other side of the front end of the flexible chest strap (1). A control box (9) is installed on the outer wall of the flexible shoulder strap (4). A wire (10) is installed at the upper end of the control box (9), and a breath sound acquisition mechanism (11) is installed at one end of the wire (10). The chest rise and fall acquisition mechanism (7) includes a first positioning plate (701), a lower housing (702), and an upper housing (705). The first positioning plate (701) is disposed on the outer wall of the flexible chest band (1), and the lower housing (702) is disposed on the inner wall of the flexible chest band (1). The four corners of the first positioning plate (701) are connected to the lower housing (702) by screws. The upper housing (705) is disposed above the lower housing (702), and the four corners of the lower housing (702) are... The lower housing (702) is connected to the upper housing (705) by a spring (704). A cross-shaped pressure groove (708) is provided on the upper surface of the lower housing (702). A pressure transmission column (703) is installed at the middle position of the lower end of the upper housing (705). Flexible thin film pressure sensors (707) are provided on all four sides of the outer wall of the pressure transmission column (703), and the flexible thin film pressure sensors (707) are distributed in a cross shape. A fitting cover (709) is provided at the upper end of the upper housing (705). The lung sound acquisition mechanism (8) includes a second positioning plate (801), a base (802), and a heart sound sensor (803). The second positioning plate (801) is disposed on the outer wall of the flexible chest band (1), the base (802) is disposed on the inner wall of the flexible chest band (1), and the four corners of the second positioning plate (801) are connected to the base (802) by screws. The heart sound sensor (803) is disposed at the lower end of the base (802). The breathing sound acquisition mechanism (11) includes a terminal block (111), a rotating arm support (113), a first rotating arm (114), a second rotating arm (115), a collector (116), and a horn-shaped microphone (117). The rotating arm support (113) is installed on the outer wall of the terminal block (111), the first rotating arm (114) is installed at one end of the terminal block (111), the second rotating arm (115) is installed at one end of the first rotating arm (114), the collector (116) is installed at one end of the second rotating arm (115), and the horn-shaped microphone (117) is installed at one end of the collector (116). The control box (9) is internally equipped with an AD conversion module, a main control module, a power supply module, a WIFI module, and an FPGA code module; The FPGA code module is mainly divided into three modules: a driver module, a data synthesis module, and an instruction receiving and processing module. The device operates by automatically configuring upon power-on, and then controlling the data acquisition switch by sending instruction signals from the host computer to the slave computer. The specific workflow is as follows: When the device is powered on, the lower-level machine automatically configures the WIFI module and initializes the AD chip. The upper-level machine opens the serial port channel, configures the main WIFI module, and then begins to search for and connect to the WIFI module signal. Once the WIFI module is successfully connected, both the host computer and the slave computer will send a flag signal. At this time, the host computer presses the start measurement button, and the lower computer instruction receiving and processing module receives the data. According to the instruction type, it will send the corresponding instruction signal to the data integration module and the driver module. At this time, the data integration module will clear the FIFO buffer to prepare to store the data, and the driver module will give the AD signal to start the measurement. After the measurement begins, the data from the three channels will be stored in the corresponding FIFOs. The data integration module will determine the amount of data through the flag signal of the FIFO and control the data to be packaged and sent to the sending module at certain time intervals and in a certain format. The host computer receives, unpacks, classifies, and calculates the data, and then displays it visually.

2. The respiratory monitoring device according to claim 1, characterized in that: A transmission column limiting groove (710) is provided at the middle position inside the cross-shaped pressure groove (708), and a limiting column (706) is provided on the inner side of the spring (704).

3. A respiratory monitoring device according to claim 2, characterized in that: The rotating arm support (113), the first rotating arm (114), the second rotating arm (115) and the collector (116) are rotatably connected by a damping shaft (118).

4. A respiratory monitoring device according to claim 3, characterized in that: Both sides of the terminal block (111) are provided with strap connecting buckles (112), and the strap connecting buckles (112) on both sides are inclined inward.

5. A respiratory monitoring device according to claim 4, characterized in that: One end of the flexible chest strap (1) is fitted with a fold-over fold (2), and the other end of the flexible chest strap (1) is fitted with a Velcro closure (3). The Velcro closure (3) extends through and into the interior of the fold-over fold (2) and is bonded to the flexible chest strap (1). A fastening buckle (5) is fitted on the outer wall of the other end of the flexible shoulder strap (4). A connecting strap (6) is fitted on the outer wall of the fastening buckle (5), and one end of the connecting strap (6) is sewn to the inner wall of the flexible chest strap (1).

6. A method for operating a respiratory monitoring device, implemented based on the respiratory monitoring device of claim 5, characterized in that, Includes the following steps: Step 1: The person to be monitored first wears the chest rise and fall acquisition mechanism (7) and lung sound acquisition mechanism (8) on the chest through the flexible chest strap (1) and flexible shoulder strap (4). Then, the person wears the device on the head using the elastic straps on the two side straps connecting buckles (112) of the breath sound acquisition mechanism (11). By rotating the first rotating arm (114) and the second rotating arm (115), the horn-shaped microphone (117) is rotated to the mouth, thus completing the wearing of the device. Step 2: Start the device and collect the intensity of breath sounds through the horn-shaped microphone (117) placed at the mouth, collect the changes in chest rise and fall through the flexible thin-film pressure sensor (707) placed on the chest, and collect lung sounds through the heart sound sensor (803) placed on the front of the lungs on the chest, thereby obtaining three physiological signals from different parts of the human body. Each signal is converted into a digital signal through the AD conversion module after passing through the corresponding conditioning circuit. Step 3: The FPGA code module controls the three AD chips in parallel to read, integrate, and classify the data; Step 4: After integration, the FPGA code module further processes the data across clock cycles, packages it, and sends it to the host computer software via the WIFI module through the control data flow. Step 5: The host computer unpacks and classifies the data, restores the data according to the corresponding data calculation method, and displays and analyzes the data.

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