Human body instability early warning device based on surface muscle pressure monitoring
By monitoring the human body's physical disappear early warning device based on surface muscle pressure monitoring, the airbags and micro pressure difference sensor monitor muscle changes, solve the problem of expensive and inconvenient use in the existing technologies, and achieve a convenient and accurate physical loss monitoring and monitoring. Early warning.
Patent Information
- Application Number
- CN202420589107.3
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- Filing Date
- 2024-03-25
- Publication Date
- 2025-01-28
- Estimated Expiration
- 2034-03-25
AI Technical Summary
The prior art requires professional devices when judging the instability of human body, which is expensive and inconvenient to use.
Provide a human body dishonesty -based early warning device based on surface muscle pressure monitoring. The pressure difference is formed by the first airbag, the second airbag component and the micro pressure difference sensor. Essence
It has achieved convenience and accurate judgment of muscle changes, reduced the cost of device, is convenient to use, and has good application value.
Smart Images
Figure CN222398418U_ABST
Abstract
Description
Technical Field
[0001] The utility model relates to the technical field of instruments and equipment, and in particular to a human body instability early warning device based on surface muscle pressure monitoring. Background Art
[0002] The process of muscle contraction and relaxation will be manifested as changes in surface muscle pressure on the corresponding skin surface, and the micro-pressure difference sensor monitors the changes in the air pressure difference between the spherical airbag and the pressure cuff. If you want to monitor the changes in the surface muscle pressure of the corresponding skin through the air pressure difference between the airbags to achieve muscle activity monitoring, you must find the corresponding relationship between the air pressure difference signal and the surface muscle pressure signal. Most existing devices directly test the electromyographic signal to determine the muscle changes and thus determine the instability of the human body, but this requires professional equipment, is expensive, and is inconvenient to use.
[0003] In this regard, there is an urgent need to provide a device that can conveniently and accurately determine muscle changes and thus determine the instability of the human body. Utility Model Content
[0004] In order to solve the deficiencies existing in the above-mentioned prior art, the utility model provides a human body instability warning device based on surface muscle pressure monitoring, including a first airbag, a second airbag assembly, a trachea, a micro-pressure differential sensor, and a data acquisition and processing module; the housing of the micro-pressure differential sensor is provided with a first airbag interface and a second airbag interface, the first airbag is connected to the first airbag interface through the trachea, the second airbag assembly is connected to the second airbag interface through the trachea, the micro-pressure differential sensor collects the air pressure values of the first airbag and the second airbag assembly, the micro-pressure differential sensor is electrically connected to the data acquisition and processing module, and the data processing module receives the air pressure value calculated by the micro-pressure differential sensor to perform a warning of human body instability.
[0005] In one embodiment, the data acquisition and processing module includes a sensor board and a main control board. The sensor board and the main control board are electrically connected. The sensor board collects the air pressure difference measured by the micro-pressure difference chip and transmits the air pressure difference to the main control board.
[0006] In one embodiment, the main control board includes a single-chip microcomputer and a conversion chip, the output end of the single-chip microcomputer is connected to the input end of the conversion chip, the output end of the conversion chip is connected to the host computer, and the air pressure difference is processed by the single-chip microcomputer and the conversion chip and transmitted to the host computer.
[0007] In one embodiment, the model of the sensor board is ADS1256 analog-to-digital converter, the model of the single-chip microcomputer is STM32F030C8T6, and the model of the conversion chip is CH340G.
[0008] In one embodiment, the second airbag assembly includes an integrated airbag cuff, an inflation tube, a joint and Velcro, the inflation tube is connected to the airbag cuff via the joint, and the Velcro is fixed to both sides of the integrated airbag cuff.
[0009] In one embodiment, the length of the integrated airbag cuff is 50 cm, and the width of the integrated airbag cuff is 14 cm.
[0010] In one embodiment, the outer layer of the integrated airbag cuff is made of polyester fabric, and the inner layer is made of a rubber airbag.
[0011] In one embodiment, the first airbag is a spherical airbag, and the inner diameter of the blowing port of the spherical airbag is 6 mm and the outer diameter is 11 mm.
[0012] In one embodiment, the inner diameter of the trachea is 5 mm, and the outer diameter of the trachea is 8 mm.
[0013] In one embodiment, the outer diameters of the first airbag interface and the second airbag interface are 6.2 mm.
[0014] Based on the above, compared with the prior art, the utility model provides a human body instability warning device based on surface muscle pressure monitoring. A pressure difference is formed by the first airbag and the second airbag assembly. The micro-pressure difference sensor collects the pressure difference and transmits it to the data acquisition and processing module for processing. The data acquisition and processing module uploads the processed data to the host computer, and then obtains the muscle change situation to monitor and warn the instability state of the human body. The device is easy to use and low in cost, and has good application value.
[0015] Other features and beneficial effects of the utility model will be described in the subsequent description, and partly become apparent from the description, or understood by practicing the utility model. The purpose and other beneficial effects of the utility model can be achieved and obtained by the structures specifically pointed out in the description, claims and drawings. BRIEF DESCRIPTION OF THE DRAWINGS
[0016] In order to more clearly illustrate the embodiments of the utility model or the technical solutions in the prior art, the following is a brief introduction to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the utility model. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work. The positional relationships described in the drawings in the following description are based on the directions of the components shown in the diagrams unless otherwise specified.
[0017] Figure 1 A schematic diagram of the structure of a human body instability early warning device based on surface muscle pressure monitoring provided by an embodiment of the utility model;
[0018] Figure 2 A schematic diagram of a human body instability early warning device based on surface muscle pressure monitoring provided by an embodiment of the utility model;
[0019] Figure 3 A cross-sectional schematic diagram of a human body instability warning device based on surface muscle pressure monitoring provided by an embodiment of the utility model;
[0020] Figure 4 The experimental data fitting curve diagram of the relationship between elbow angle and pressure difference provided by the present invention;
[0021] Figure 5 This is a curve diagram of the relationship between elbow angle and pressure difference provided by the present invention.
[0022] Reference numerals:
[0023] First airbag 100 Integrated airbag cuff 210 Inflatable tube 220
[0024] Micro differential pressure sensor 300 Data acquisition and processing module 400 Air pipe 500 DETAILED DESCRIPTION
[0025] In order to make the purpose, technical solutions and advantages of the embodiments of the utility model clearer, the technical solutions in the embodiments of the utility model will be clearly and completely described below in conjunction with the drawings in the embodiments of the utility model. Obviously, the described embodiments are part of the embodiments of the utility model, rather than all of the embodiments; the technical features designed in different implementation modes of the utility model described below can be combined with each other as long as they do not conflict with each other; based on the embodiments in the utility model, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the utility model.
[0026] In the description of the present invention, it should be noted that all terms (including technical terms and scientific terms) used in the present invention have the same meanings as those generally understood by ordinary technicians in the field to which the present invention belongs, and cannot be understood as limitations on the present invention; it should be further understood that the terms used in the present invention should be understood to have meanings consistent with the meanings of these terms in the context of this specification and in the relevant fields, and should not be understood in an idealized or overly formal sense, unless explicitly defined in this utility model.
[0027] A human body instability early warning device based on surface muscle pressure monitoring, such as Figure 1As shown, it includes a first airbag 100, a second airbag assembly, an trachea 500, a micro-pressure differential sensor 300, and a data acquisition and processing module 400; the shell of the micro-pressure differential sensor 300 is provided with a first airbag interface and a second airbag interface, the first airbag 100 is connected to the first airbag interface through the trachea 500, and the second airbag assembly is connected to the second airbag interface through the trachea 500, the micro-pressure differential sensor 300 collects the air pressure values of the first airbag 100 and the second airbag assembly, the micro-pressure differential sensor 300 is electrically connected to the data acquisition and processing module 400, and the data processing module receives the air pressure value calculated by the micro-pressure differential sensor 300 to provide an early warning of human body instability.
[0028] In specific implementation, the system monitoring part is composed of the first airbag 100, the second airbag assembly and the micro-pressure difference sensor 300, which are connected by the trachea 500 with an inner diameter of 5mm and an outer diameter of 8mm, and the trachea 500 is a silicone rubber hose. During operation, the first airbag 100 and the second airbag assembly are fixed to a certain part of the human limb, and the surface muscle pressure change of the part is calculated by measuring the air pressure difference between the airbags to monitor muscle activity.
[0029] Preferably, the micro differential pressure sensor 300 adopts the LFM108 series micro differential pressure sensor 300 produced by Zhejiang Lifu Sensing Technology Co., Ltd., with a range of ±5kPa, an accuracy of ±1%FS, and an RS-485 communication interface. The micro differential pressure sensor 300 can directly monitor and output the air pressure difference between the two input signals, and the differential transmission method is adopted, so that it has many advantages such as fast response speed, high monitoring accuracy and strong anti-interference. Compared with the traditional single-channel air pressure sensor, it is more suitable for surface muscle pressure monitoring. In the monitoring part of the system, the second airbag assembly is connected to the positive end of the micro differential pressure sensor 300, and the first airbag 100 is connected to the negative end of the micro differential pressure sensor 300. The micro differential pressure sensor 300 also includes an RS485 interface, which is connected to the data acquisition and processing module 400 through the RS485 bus.
[0030] In the present invention, the changes in the target muscle pressure on the skin surface are mainly collected by the first airbag 100 and the second airbag assembly, which are all the parts of the device that need to be in direct contact with the human skin during wearing. Therefore, before establishing a physical model of the contact between the first airbag 100, the second airbag assembly and the target muscle's corresponding skin surface in the system monitoring part, it is necessary to first determine the relative positional relationship between the first airbag 100, the second airbag assembly and the target muscle, and then model it according to the specific positional relationship.
[0031] In one embodiment, the data acquisition and processing module 400 includes a sensor board and a main control board, the sensor board and the main control board are electrically connected, the sensor board collects the air pressure difference measured by the micro-pressure difference chip, and transmits the air pressure difference to the main control board. The main control board includes a single-chip microcomputer and a conversion chip, the output end of the single-chip microcomputer is connected to the input end of the conversion chip, the output end of the conversion chip is connected to the host computer, and the air pressure difference is processed by the single-chip microcomputer and the conversion chip and transmitted to the host computer. The model of the sensor board is ADS1256 analog-to-digital converter, the model of the single-chip microcomputer is STM32F030C8T6, and the model of the conversion chip is CH340G.
[0032] In specific implementation, the data acquisition system is divided into two parts: the sensor board and the main control board. The sensor board uses an analog-to-digital converter of model ADS1256 to collect the air pressure difference measured by the micro-pressure difference chip, and the sensor board includes at least one sensor. Multiple sensors can also be configured as required. The sensor board integrates multiple sensors. The main control board uses a single-chip microcomputer of model STM32F030C8T6 and a conversion chip of model CH340G to process data, and sends it to the host PC through the USB interface for display using the serial port assistant XCOM software.
[0033] In one embodiment, the second airbag assembly includes an integrated airbag cuff 210 , an inflation tube 220 , a joint and Velcro, the inflation tube 220 is connected to the integrated airbag cuff 210 via the joint, and the Velcro is fixed to both sides of the integrated airbag cuff 210 .
[0034] Preferably, the integrated air bag cuff 210 has a length of 50 cm and a width of 14 cm. It is provided with two 50 cm long inflation tubes 220, a joint / interface, a ball valve and Velcro, and can be wrapped around one of the four limbs of a person and fixed.
[0035] Furthermore, the outer layer of the integrated airbag cuff 210 is made of polyester fabric, and the inner layer is made of rubber airbag. Both materials are relatively soft and conducive to direct contact with the skin.
[0036] In one embodiment, the first airbag 100 is a spherical airbag, and the inner diameter of the blowing port of the spherical airbag is 6 mm and the outer diameter is 11 mm.
[0037] During specific implementation, a spherical airbag is placed between the airbag cuff and the limb, and is made of rubber. The inner diameter of the air inlet is 6 mm, and the outer diameter is 11 mm.
[0038] In one embodiment, the outer diameters of the first airbag interface and the second airbag interface are 6.2 mm.
[0039] In the specific implementation, the micro-pressure difference chip used has two air pipe 500 interfaces with an outer diameter of 6.2 mm, a measuring range of ±20 kPa, and a resolution of 1 Pa.
[0040] The specific wearing and working process is as follows: 1. When wearing the device, if Figure 2 and Figure 3 As shown, first, the spherical airbag is placed tightly against the belly of the muscle to be monitored, and then the integrated airbag cuff 210 is wrapped around the spherical airbag and the periphery of the limb and fixed with Velcro, so that the spherical airbag is located between the belly of the muscle to be monitored and the integrated airbag cuff 210. During the use of the device, the spherical airbag will be squeezed and rubbed from both the integrated airbag cuff 210 and the muscle, so it will always be in the original wearing position without relative sliding. Therefore, the relative position relationship between the spherical airbag, the integrated airbag cuff 210 and the target muscle does not change during the entire monitoring process.
[0041] 2. Place the spherical airbag in the above device on the biceps brachii of the upper arm, and at the same time stick the electrode of the EMG sensor on the same position to collect the electromyographic signal of the limbs, and then tie the integrated airbag cuff 210 to the outer periphery of the spherical airbag of the upper arm.
[0042] During the specific implementation, the limb electromyographic signals are collected using a dual-lead electromyographic EMG kit produced by Wuxi Sizhirui Technology Co., Ltd. The collected signals are sent to the PC via a BLE Bluetooth 4.0 adapter and displayed using the matching dual-lead electromyographic software.
[0043] 3. Connect the data acquisition and processing module 400 to the PC to display the air pressure difference data, and connect the EMG sensor to the PC via a BLE Bluetooth 4.0 adapter to display the electromyographic signal.
[0044] 4. Adjust the initial pressure difference between the spherical airbag and the integrated airbag cuff 210 to about 0Pa, let the biceps brachii perform isometric contraction and compare the pressure difference signal with the electromyographic signal, and then let the biceps brachii perform isotonic contraction and compare the pressure difference signal with the electromyographic signal. It is found that the trend of the pressure difference signal is consistent with the electromyographic signal, and has a smoother waveform and a higher amplitude signal value, which verifies the effectiveness of this method in monitoring muscle activity.
[0045] 5. Place the airbag a in the above device on the biceps brachii of the upper arm, and tie the integrated airbag cuff 210 to the periphery of the spherical airbag of the upper arm.
[0046] 6. Let the arm hang naturally, and adjust the initial pressure difference between the airbags to about 0Pa. Fix the upper arm, bend the forearm with the elbow joint as the fixed point, record the pressure difference during the bending process, and use a digital angle ruler to measure the arm bending angle.
[0047] 7. After repeating the experiment many times, the arm bending angle and air pressure difference were fitted using the polynomial fitting function based on the least squares method in MATLAB for each experiment. It was found that the relationship curves obtained in each experiment were highly consistent, which verified the effectiveness of this method for action recognition.
[0048] 8. Place the spherical airbag in the above device on the gastrocnemius muscle of the calf, and tie the integrated airbag cuff 210 to the periphery of the spherical airbag of the calf.
[0049] 9. In the initial state, the patient maintains a standing posture and adjusts the initial air pressure difference between the spherical airbag and the integrated airbag cuff 210 to about 0Pa. Then, the patient performs sitting down and standing up movements and collects and records the air pressure difference curve.
[0050] 10. The standing up and sitting down cycles were repeated many times, and the pressure difference curves obtained by recording each cycle were compared. It was found that the curves were highly consistent, which verified the effectiveness of this method for action recognition.
[0051] Previous experiments have verified that this method can be used for motion recognition by monitoring muscle activity, so the above-mentioned device can be worn on the gastrocnemius muscle of the calf, and a data acquisition system can be used to monitor muscle activity in real time to build a human body instability early warning system.
[0052] 11. The spherical airbag in the above device is placed on the gastrocnemius muscle of the calf, and the integrated airbag cuff 210 is tied to the periphery of the spherical airbag of the calf. The air tube 500 is used to connect the micro-pressure difference chip and the two airbags to measure the pressure difference between them. The measurement signal output by the micro-pressure difference chip is collected by the analog-to-digital converter and sent to the single-chip microcomputer for processing.
[0053] 12. The microcontroller monitors muscle activity by real-time processing of the pressure difference signal between the airbags, and drives the buzzer to sound an early warning when it detects body instability.
[0054] In addition, those skilled in the art should understand that, although there are many problems in the prior art, each embodiment or technical solution of the utility model can be improved in only one or several aspects, without having to solve all the technical problems listed in the prior art or background technology at the same time. Those skilled in the art should understand that the content not mentioned in a claim should not be used as a limitation on the claim.
[0055] During the specific implementation, the utility model designed and conducted a practical verification experiment of the device. In the experiment, the isotonic contraction activity of the biceps brachii during elbow flexion and extension was monitored by the device, and the elbow bending angle was measured and recorded using a digital angle ruler. After analyzing and studying the relationship between the elbow bending angle and the air pressure difference, it was found that under ideal conditions, the device can be used to accurately estimate the elbow bending angle. The discovery of the relationship between the elbow bending angle and the pressure difference also proves that the data obtained when using the device to monitor muscle activity can be used to reflect the movement state of human limbs, indicating that the device has the potential to act as a posture recognition system in daily life and thus be used for sports and daily protection, and the practicality of the device has therefore been verified.
[0056] The angle ruler used in this experiment is an electronic digital angle ruler model SYLF200J produced by Zhejiang Deqing Shengtaixin Electronic Technology Co., Ltd. This angle ruler can achieve 360-degree measurement, with a resolution of 0.05 degrees, a tolerance range of ±0.3 degrees, and is powered by a 3V button battery. The device for acquiring the air pressure difference signal in the practicality verification experiment is the same as that used in the previous validity verification experiment, and the RS485-USB converter and Modbus Poll software are also used for signal transmission and data monitoring.
[0057] In the experiment, the relationship between the elbow bending angle and the air pressure difference signal was calculated using the polyfit curve fitting function in MATLAB. A polynomial function can be constructed based on the least squares method for a discrete data point set, so that the curve of the function is as close to the known data points as possible. The curve fitting effect was verified using the Curve Fitting Tool in MATLAB, which can provide four parameters including the coefficient of determination to help users verify the approximation of the obtained fitting curve to the input data.
[0058] Because the biceps brachii plays an irreplaceable role in the bending and extension of the elbow, the biceps brachii of the right upper arm of the experimental subject was selected as the target muscle in this experiment. The device was worn on the upper arm to monitor the air pressure difference signal generated by the isotonic contraction of the biceps brachii in real time during the experiment. At the same time, a digital angle ruler was used to measure and record the elbow bending angle corresponding to the real-time air pressure difference. Figure 4 Then the polyfit function in MATLAB is used to fit the processed data into a 4th-order polynomial function, and finally the special bending angle of the elbow is used to verify the obtained expression to prove that there is a functional relationship between the elbow bending angle and the air pressure difference.
[0059] The experimental subject in this experiment is a healthy adult male with muscle content within the normal range for men, no disability and no limb impairment. During the experiment, the experimental subject always maintains an upright posture and should minimize body shaking. The experiment is conducted in a well-lit room without any interference, and the ambient temperature is about 26 degrees Celsius. Before the experiment begins, use a ball valve to inflate the pressure cuff until the airbag can be fixed on the skin surface corresponding to the target muscle and the initial air pressure difference is stabilized at about 0 Pa. During the experiment, the experimenter's right arm is bent from a naturally hanging fully extended state to a 90-degree angle between the forearm and the upper arm as an experimental cycle. In each cycle, the elbow bending angle is randomly selected to record the corresponding air pressure difference. A total of three sets of experimental cycles are carried out to reduce accidental errors and find general rules. Tables 1, 2 and 3 show the data obtained from the three sets of experiments.
[0060] Table 1 The first set of experimental data on the relationship between elbow bending angle and pressure difference
[0061]
[0062] Table 2 The second set of experimental data on the relationship between elbow bending angle and pressure difference
[0063]
[0064] Table 3 The third group of experimental data on the relationship between elbow bending angle and pressure difference
[0065]
[0066]
[0067] It should be noted that, since the micro-pressure differential sensor used in this device has high accuracy and the muscle tissues in various parts of the human body cannot remain absolutely static, the air pressure differential signal collected when monitoring the activity of the biceps brachii will always be in a fluctuating state, so 5 corresponding air pressure differential values are selected and recorded at each elbow bending angle. The three sets of experimental data were fitted with a 4th-order polynomial using the polyfit function in MATLAB, and the three fitted function curves are shown as follows: Figure 4 As shown in the figure, the determination coefficients of the three fitting curves are 0.9975, 0.9973 and 0.9997, respectively, which proves that the fitting degree is good. Figure 4 It can be observed that the trends of the three fitted curves are basically the same. The pressure difference increases with the increase of the elbow bending angle. The errors between the data points on each curve are within the acceptable range. Therefore, the data obtained from the three groups of experiments can be combined and fitted into a function curve using the polyfit function. Figure 5As shown, the coefficient of determination of the fitting curve is 0.9908, which proves that the fitting degree is good. The expression corresponding to the curve is the following formula (2.17), which can represent the mapping relationship between the elbow bending angle and the air pressure difference established by the device through experiments, specifically:
[0068] y=-8.3747×10 -5 x 4 +0.0223x 3 -1.6101x 2 +46.3793x-412.9338 (2.17)
[0070] Finally, take the special bending angle of the elbow and conduct another set of experiments with the same steps as above. Compare the obtained data with the pressure difference calculated by formula (2.17) and calculate the relative error by formula (2.18) to verify the relationship between the elbow bending angle and the pressure difference. The verification results are shown in Table 4, and the obtained fitting curve is shown in Figure 5 As shown in the figure, it can be seen that the relative error between the theoretical calculated value and the actual measured value of the air pressure difference signal at each special elbow bending angle can be controlled within 6% and decreases with the increase of the elbow bending angle, which proves that the obtained expression can accurately reflect the corresponding relationship between the elbow bending angle and the air pressure difference. The device can be used to accurately estimate the elbow bending angle. The discovery of this relationship also brings inspiration to the expansion of the use of this device, confirming its potential to serve as a posture recognition system in daily life, and further verifying the practicality of the device.
[0071]
[0072] Table 4 Verification results of the relationship between elbow bending angle and pressure difference
[0073]
[0074] The utility model firstly establishes a physical model of the contact between the system monitoring part of the airbag and the skin surface corresponding to the target muscle. While proving the linear correlation between the air pressure difference signal and the surface muscle pressure signal, it also provides a theoretical basis for the device to realize the surface muscle pressure monitoring of a certain point on the muscle under ideal conditions. Then, the effectiveness verification experiment with the brachioradialis and biceps brachii as the target muscles was designed and carried out. By comparing with the electromyography method, it was confirmed that the device has good accuracy, sensitivity and stability for both isometric and isotonic contraction of muscles. Finally, by studying the relationship between the elbow bending angle and the air pressure difference, it was proved that the use of this device can realize the accurate estimation of the elbow bending angle, and at the same time, the practicability of the device was further verified, which laid a good foundation for its application in the fields of sports protection and action recognition.
[0075] Although the terms such as first airbag, second airbag assembly, integrated airbag cuff, inflation tube, micro-pressure difference sensor, data acquisition and processing module, trachea, etc. are used more frequently in this article, the possibility of using other terms is not excluded. The use of these terms is only to more conveniently describe and explain the essence of the utility model; interpreting them as any additional restrictions is contrary to the spirit of the utility model; the terms "first", "second", etc. (if any) in the description and claims of the embodiment of the utility model and the above-mentioned drawings are used to distinguish similar objects, and are not necessarily used to describe a specific order or sequence.
[0076] Finally, it should be noted that the above embodiments are only used to illustrate the technical solution of the utility model, rather than to limit it. Although the utility model has been described in detail with reference to the aforementioned embodiments, ordinary technicians in this field should understand that they can still modify the technical solutions recorded in the aforementioned embodiments, or replace some or all of the technical features therein with equivalents. However, these modifications or replacements do not make the essence of the corresponding technical solution deviate from the scope of the technical solution of the embodiments of the utility model.
Claims
1. A human body instability early warning device based on surface muscle pressure monitoring, characterized in that: It includes a first airbag, a second airbag assembly, an air tube, a micro-pressure difference sensor, and a data acquisition and processing module; The housing of the micro-pressure differential sensor is provided with a first airbag interface and a second airbag interface. The first airbag is connected to the first airbag interface through the trachea, and the second airbag assembly is connected to the second airbag interface through the trachea. The micro-pressure differential sensor collects the air pressure values of the first airbag and the second airbag assembly. The micro-pressure differential sensor is electrically connected to the data acquisition and processing module, and the data processing module receives the air pressure value calculated by the micro-pressure differential sensor to provide an early warning of human body instability.
2. The human body instability early warning device based on surface muscle pressure monitoring according to claim 1 is characterized in that: The data acquisition and processing module includes a sensor board and a main control board. The sensor board is electrically connected to the main control board. The sensor board collects the air pressure difference measured by the micro-pressure difference chip and transmits the air pressure difference to the main control board.
3. The human body instability early warning device based on surface muscle pressure monitoring according to claim 2 is characterized in that: The main control board includes a single-chip microcomputer and a conversion chip. The output end of the single-chip microcomputer is connected to the input end of the conversion chip. The output end of the conversion chip is connected to a host computer. The air pressure difference is processed by the single-chip microcomputer and the conversion chip and transmitted to the host computer.
4. The human body instability early warning device based on surface muscle pressure monitoring according to claim 3 is characterized in that: The model of the sensor board is ADS1256 analog-to-digital converter, the model of the single-chip microcomputer is STM32F030C8T6, and the model of the conversion chip is CH340G.
5. The human body instability early warning device based on surface muscle pressure monitoring according to claim 1 is characterized in that: The second airbag assembly includes an integrated airbag cuff, an inflation tube, a joint and Velcro, the inflation tube is connected to the airbag cuff through the joint, and the Velcro is fixed to both sides of the integrated airbag cuff.
6. The human body instability early warning device based on surface muscle pressure monitoring according to claim 5 is characterized in that: The length of the integrated airbag cuff is 50 cm, and the width of the integrated airbag cuff is 14 cm.
7. The human body instability early warning device based on surface muscle pressure monitoring according to claim 5 is characterized in that: The outer layer of the integrated air bag cuff is made of polyester cloth, and the inner layer is made of rubber air bag.
8. The human body instability early warning device based on surface muscle pressure monitoring according to claim 1 is characterized in that: The first airbag is a spherical airbag, and the inner diameter of the blowing port of the spherical airbag is 6 mm and the outer diameter is 11 mm.
9. The human body instability early warning device based on surface muscle pressure monitoring according to claim 1, characterized in that: The inner diameter of the trachea is 5 mm, and the outer diameter of the trachea is 8 mm.
10. The human body instability early warning device based on surface muscle pressure monitoring according to claim 1, characterized in that: The outer diameters of the first airbag interface and the second airbag interface are 6.2 mm.