Fabric electronic system for muscle fatigue detection and treatment integration

Abstract

The application discloses a muscle fatigue detection and treatment integrated fabric electronic system, which is integrated with conductive fabric lines and physiological electrodes, vertical interconnection through holes and patch type components on the same fabric substrate, and is provided with conductive fabric lines on both side surfaces of the fabric substrate and is communicated with each other through the vertical interconnection through holes, and the overall formed circuit comprises an electrode array and a signal conditioning circuit, wherein the electrode array is used for detecting electromyographic signals and applying transcutaneous electrical stimulation, the signal conditioning circuit is used for amplifying electromyographic signals, conditioning electrical stimulation waveforms and overall timing logic control, and has the functions of safety isolation and electrical stimulation waveform detection. The application can highly integrate components on a single fabric through process design, and realizes electromyographic signal acquisition and transcutaneous electrical stimulation. It is verified through experiments that the system can be worn on an arm to monitor the fatigue process of the biceps brachii and effectively promote fatigue recovery, and demonstrates its ability in closed-loop diagnosis and treatment.

Description

Technical Field

[0001] This invention belongs to the field of intelligent electronic fabric technology and relates to a fabric electronic system that integrates muscle fatigue detection and treatment. Background Technology

[0002] Textiles with electronic components offer a portable and personalized approach to health monitoring and treatment. However, existing solutions often fail to integrate layered circuitry and high-density chips onto or within textiles, typically requiring external commercial circuit boards, which hinders system-level portability and wearability comfort.

[0003] We used a laser-integrated manufacturing process to achieve tight integration of dual-layer circuits, electrodes, and flexible sensors on a single piece of fabric, facilitating the realization of wireless, wearable, and breathable health electronic systems. Based on this, this invention further designs a wireless, monolithically integrated, breathable, wearable fabric electronic system to address the integrated detection and treatment needs of precision medicine, capable of simultaneously monitoring and alleviating muscle fatigue. The overall circuit area in this fabric electronic system can be less than 50 cm². 2 It can be worn on parts of the body such as the biceps and quadriceps to exert its effects.

[0004] Compared to existing technologies, this invention enables signal processing and wireless transmission without the need for external commercial circuit boards, and features excellent breathability and wearing comfort. Furthermore, it can not only detect physiological signals but also apply transcutaneous electrical stimulation to muscles to relieve muscle fatigue, thus achieving integrated detection and treatment. Summary of the Invention

[0005] The purpose of this invention is to address the shortcomings of existing technologies by providing a fabric electronic system that integrates muscle fatigue detection and treatment. This fabric electronic system integrates functional fabric, flexible electronic components, rigid electronic components, conductive fabric threads, and physiological electrodes on both sides of a single piece of fabric, enabling monitoring and treatment to be integrated, and has great potential in closed-loop diagnosis and treatment.

[0006] The technical solution adopted in this invention is as follows:

[0007] A fabric electronic system integrating muscle fatigue detection and treatment integrates conductive fabric threads, physiological electrodes, vertical interconnect vias, and patch components on the same fabric substrate. Conductive fabric threads are provided on both sides of the fabric substrate and are interconnected with each other through vertical interconnect vias. The overall circuit includes an electrode array and a signal conditioning circuit. The electrode array is used to detect electromyographic signals and to apply transcutaneous electrical stimulation. The signal conditioning circuit is used for amplifying electromyographic signals, conditioning the electrical stimulation waveform, and controlling the overall timing logic. It also has the functions of safety isolation and electrical stimulation waveform detection.

[0008] In the above technical solution, the electrode array is further constructed by multiplexing a single pair of electrodes. The electrode array includes electrodes 1 to 4, wherein electrodes 1 and 2 are the positive and negative input terminals of electromyography signals, electrode 3 is the positive output terminal of electrical stimulation, and electrode 4 serves as both the negative output terminal of electrical stimulation and the output terminal of the right leg drive circuit. The electrodes used for signal sampling are separated from the electrodes used for applying electrical stimulation to avoid the influence of electrode polarization on signal sampling.

[0009] Furthermore, the signal conditioning circuit uses three independent optocouplers and an H-bridge circuit composed of four optocouplers. Electrodes 1, 2, and 4 are each connected to the peripheral circuit through an independent optocoupler, while electrodes 3 and 4 are connected to the peripheral circuit through the H-bridge circuit. By controlling the optocouplers, the four electrodes are selectively connected to the circuit to achieve switching between two modes: electromyography detection and electrical stimulation.

[0010] Furthermore, the signal conditioning circuit uses a constant current source to output the stimulation current. The amplitude of the stimulation current is controlled by the digital-to-analog converter of the microcontroller, and the direction of the stimulation current is controlled by the H-bridge circuit at the load end of the constant current source. The duty cycle, frequency, and amplitude of the stimulation current are all adjustable in real time to ensure that the output is electrically neutral.

[0011] Furthermore, in the electrical stimulation mode, the independent optical couplers connected to electrodes 1, 2, and 4 are all blocked, and the optical couplers in the H-bridge circuit are switched on and off in an orderly manner; in the electromyography detection mode, the optical couplers in the H-bridge circuit are blocked, and the independent optical couplers connected to electrodes 1, 2, and 4 are all normally open.

[0012] Furthermore, the vertical interconnecting vias are the parts of the fabric substrate where vias need to be formed to connect the circuits on both sides of the fabric. The conductive paste is infiltrated into the texture structure of the fabric substrate in this part by using the air pressure injection method, so that the corresponding area of ​​the fabric substrate can achieve front and back connection.

[0013] Furthermore, the conductive fabric thread and physiological electrode are formed by cutting the conductive fabric according to a pre-designed pattern using a laser. Then, the conductive fabric thread and physiological electrode are transferred to both sides of the fabric substrate using a transfer method. The conductive fabric thread and physiological electrode on both sides are connected through the vertical interconnecting via.

[0014] Furthermore, the surface-mount components are soldered onto conductive fabric wires using solder paste to form a complete circuit.

[0015] Furthermore, on the lower surface of the fabric substrate, there are conductive fabric threads and physiological electrode layers, as well as medical double-sided adhesive and hydrogel layers in sequence; the medical double-sided adhesive and hydrogel layers are formed by laser cutting of medical double-sided adhesive to form grooves of the same shape as each physiological electrode, and hydrogel precursor liquid is injected into the grooves and cured by ultraviolet light; conductive fabric threads and patch electronic devices are distributed on the upper surface of the fabric substrate.

[0016] The present invention has the following beneficial effects:

[0017] 1. The present invention achieves the integrated integration of rigid electronic devices such as patch electronic components, flexible electronic devices such as physiological electrodes, inner and outer double-layer conductive fabric lines, and vertical interconnecting vias on the same fabric. Moreover, since the double-layer conductive circuit with independent wiring is realized on a single piece of fabric, it can allow for a higher degree of circuit layout compared with the prior art. At the same time, it can ensure that the corresponding fabric electronic system has the characteristics of breathability, wearability, and treatment safety.

[0018] 2. The solution of the present invention can simultaneously monitor and alleviate muscle fatigue without the need for an external commercial circuit board, and is used for integrated detection and treatment of muscle fatigue. Attached Figure Description

[0019] Figure 1 The diagram shows the geometric structure and cross-sectional view of the electrode array of the fabric electronic system of the present invention.

[0020] Figure 2 This is a schematic diagram of the electrode array operating mode of the fabric electronic system of the present invention.

[0021] Figure 3 This is a 3D exploded view of the fabric electronic system of the present invention.

[0022] Figure 4 These are physical images and wearable effect diagrams of the fabric electronic system of the present invention.

[0023] Figure 5 This is a program logic diagram of the fabric electronic system of the present invention in two modes: electromyography detection and application of electrical stimulation.

[0024] Figure 6 This is a functional block diagram of the fabric electronic system of the present invention.

[0025] Figure 7 The figures show the current (Fig. a) and voltage (Fig. b) generated by the fabric electronic system of the present invention when transcutaneous electrical stimulation is applied to the biceps brachii, as well as the electromyographic signal (Fig. c) and its power spectral density (Fig. d) generated when the biceps brachii contracts.

[0026] Figure 8The figures show a comparison of the current consumption of the fabric electronics system of the present invention and a commercial PCB with the same function in different modes (Figure a), as well as a comparison of the waveforms of the applied electrical stimulation (Figures b and c).

[0027] Figure 9 The electromyography (EMG) signal (Fig. a), root mean square (Fig. b), and short-time Fourier transform spectrum (Fig. c) collected by the fabric electronic system of the present invention when a 5 kg load is applied to the biceps brachii are shown.

[0028] Figure 10 The median frequency (MDF) of the electromyography signal of the fabric electronic system of the present invention during biceps fatigue and after 10 seconds of rest is statistically in the range of 5 to 160 Hz.

[0029] Figure 11 The relationship between maximum voluntary contractile force (MVC) and time during the recovery process of biceps brachii fatigue. Specific implementation methods

[0030] The fabric electronic system of the present invention will be further described below with reference to the accompanying drawings and embodiments.

[0031] This invention discloses a fabric electronics system integrating muscle fatigue detection and treatment. It integrates conductive fabric threads, physiological electrodes, vertical interconnect vias, and patch-type components on a single fabric substrate using laser-integrated manufacturing processes, pneumatic infusion processes, and transfer printing combined with welding. Conductive fabric threads are provided on both sides of the fabric substrate and interconnected through vertical interconnect vias, forming a double-layer circuit structure on a single layer of fabric. The overall circuit includes an electrode array and a signal conditioning circuit. According to a specific embodiment of the invention, the circuit also includes a wireless transmission module. Furthermore, the system includes a host computer. The electrode array is used to detect electromyographic (EMG) signals, and the median frequency of the EMG signals is used to assess the degree of muscle fatigue. Simultaneously, the physiological electrodes are used to apply transcutaneous electrical stimulation (TES) to accelerate the recovery of the muscle's maximum voluntary contractile force. The signal conditioning circuit fully considers the constraints of fabric electronics manufacturing processes and the miniaturization requirements of wearable devices. It is used for EMG signal amplification, electrical stimulation waveform conditioning, and overall timing logic control, and also has functions of safety isolation and electrical stimulation waveform detection.

[0032] The specific circuits in the fabric electronic system of the present invention can be designed accordingly based on the functions described. The fabric substrate in the fabric electronic system is one or more of modal knitted fabric, medical nonwoven fabric, polyimide (PI) fabric, or polyester taffeta woven fabric. The vertical interconnecting vias are formed on the fabric substrate according to the design drawings to connect the circuits on both sides. Specifically, the conductive paste is brushed onto both sides of the required area using a pneumatic injection method. On both sides, air is blown through an air gun to allow the conductive paste to penetrate into the texture structure of the fabric substrate at that location, so that the corresponding area of ​​the fabric substrate achieves front-to-back connection. The conductive paste used is preferably an intermetallic compound LM / Cu NP paste formed by mixing liquid metal and copper nanoparticles using a centrifugal mixer or a high-speed defoamer. The tangential force generated during centrifugation breaks the oxide film on the surface of LM, allowing LM and Cu NP to react fully during the mixing process. No additional acid, alkali, or other chemical reagents are required, resulting in uniform mixing and excellent performance. The conductive fabric threads and physiological electrodes are formed by cutting conductive fabric according to a pre-designed pattern using a laser. Then, the conductive fabric threads and physiological electrodes are transferred to both sides of a fabric substrate using a transfer method. The conductive fabric threads and physiological electrodes on both sides are connected through vertical interconnecting vias. Specifically, the following method can be used: A layer of adhesive film (AL) is pressed onto one side of a metal fabric (MT), and a layer of adhesive, water-soluble sacrificial layer (SL) is pressed onto the other side of the metal fabric, forming an AL / MT / SL structure. A patterned conductive circuit is cut into the AL and MT layers using an ultraviolet nanosecond laser, while the SL remains intact. The entire AL / MT / SL is then attached to the fabric substrate with the AL side facing out. The substrate is then immersed in water, and after the SL layer softens in the water, it is removed. The AL / MT layer attached to the fabric substrate is dried, and the excess AL / MT layer, except for the patterned conductive circuit, is peeled off to form the conductive fabric thread or physiological electrode. The surface mount components are soldered onto conductive fabric wires using solder paste to form a complete circuit. The solder paste is preferably a low-melting-point solder paste formed by mixing solder paste and aluminum flux to effectively remove the nickel oxide layer of commercial surface mount electronic components and ensure the soldering effect.

[0033] like Figure 1-11 As shown, this is a specific embodiment of the present invention, in which:

[0034] (1) An electrode array was constructed using a single pair of electrodes reused: electrodes 1, 2, and 4 were used to detect electromyographic signals, and electrodes 3 and 4 were used to apply transcutaneous electrical stimulation. The reuse of electrode 4 was achieved through an optical coupler isolator, which effectively saved area.

[0035] (2) Design of the electrical stimulation source for the fabric-based signal conditioning circuit: A constant current source is used to output the stimulation current. This constant current source is powered by a single-stage boost circuit with a BOOST topology, which converts the 3.7V lithium battery input voltage to a 40V output voltage. The amplitude of the stimulation current is controlled by the DAC (digital-to-analog converter) of the STM32L052 microcontroller. The direction of the stimulation current is controlled by the H-bridge at the load end of the constant current source, which consists of four optocouplers. Therefore, the duty cycle, frequency, and amplitude of the stimulation current are adjustable in real time to ensure a neutral output current, thereby guaranteeing the comfort and safety of the treatment.

[0036] (3) Signal acquisition design of the fabric-based signal conditioning circuit: The STM32L052's ADC (Analog-to-Digital Converter) is used to acquire electromyographic signals and electrical stimulation waveforms. The DMA (Direct Memory Access) function of the STM32L052 controls the ADC's sampling and subsequent data transmission, improving the program's real-time performance. Simultaneously, the sampling rate is switched according to different sampling signals: When acquiring electrical stimulation waveforms, since the waveforms are sparse short pulses (period 20ms, pulse duration ~3ms), the ADC in electrical stimulation mode only performs high-rate sampling (40kHz) within 3ms after the pulse occurs, and does not sample at other times, thus reducing the occupation of storage and transmission bandwidth; when acquiring electromyographic signals, the ADC continuously performs low-rate sampling (720Hz) and synchronizes with signal transmission. To improve the signal-to-noise ratio of the electromyographic signal before sampling, an instrumentation amplifier and bandpass filter are used to amplify the signal from the electrode terminals. A right leg drive circuit is used to suppress common-mode noise from the human body, and a πRC network is used to filter out power ripple noise caused by the electrical stimulation module and Bluetooth module.

[0037] (4) Safety isolation design of fabric-based signal conditioning circuit: During electrical stimulation, to prevent the low-voltage electromyography (EMG) signal sampling electrode from forming a connection with the high-voltage electrical stimulation electrode on the skin surface, an optical coupler isolator is designed at the connection point of the circuit and each electrode. In electrical stimulation mode, the optical coupler of the EMG signal sampling electrode is blocked, and the optical coupler of the electrical stimulation electrode is switched on and off in an orderly manner; in EMG signal sampling mode, the optical coupler of the electrical stimulation electrode is blocked, and the optical coupler of the EMG signal sampling electrode is normally open.

[0038] Specifically:

[0039] Figure 1 A schematic diagram of the electrode array in this example is shown. Figure 1As shown on the left, electrodes 121 and 122 are the positive and negative input terminals for electromyography (EMG) signals. Electrode 323 is the positive output terminal for electrical stimulation, and electrode 424 serves as both the negative output terminal for electrical stimulation and the output terminal of the right leg drive circuit. Electrodes 3 and 4 have excessively large output currents, which can easily cause polarization on their surfaces, reducing electrode efficiency and significantly increasing impedance. To ensure the accuracy and stability of signal acquisition, the EMG signal sampling electrodes (electrodes 1 and 2) require low impedance; therefore, they must be strictly separated from the output electrical stimulation electrodes (electrodes 3 and 4). The right leg drive circuit has lower impedance requirements and is less affected by polarization; therefore, electrode 4 can serve as both the negative output terminal for electrical stimulation and the output terminal of the right leg drive circuit. The four electrodes are compactly arranged on fabric 11, and the reuse of electrode 424 effectively improves space utilization. The shapes of the electrodes can be adjusted according to the needs of the scenario. Figure 1 As shown in the cross-sectional view on the right, the interface between the electrode and the skin uses conductive hydrogel to reduce skin-electrode impedance. Medical double-sided tape is placed around the hydrogel to ensure that the electrode can be stably attached to the skin surface during wear. Although using Ag / AgCl with low polarization impedance as the electrode material can avoid the influence of electrode polarization and enable the reuse of electromyography signal sampling electrodes (electrodes 1 and 2) and output electrical stimulation electrodes (electrodes 3 and 4), in order to improve the versatility of the material and facilitate the fabrication of patterned electrodes, thereby benefiting circuit layout, this invention selects metallized textiles and hydrogel as electrode materials.

[0040] Figure 2 A schematic diagram of the electrode array's operating modes is shown. Figure 6 This is a complete functional block diagram of the fabric electronic system in this specific example. By configuring optocouplers and an H-bridge circuit, electrodes are selectively connected to the peripheral circuit, thereby achieving different operating modes. The H-bridge consists of four optocouplers. In electromyography (EMG) detection mode, the optocouplers inside the H-bridge on the right are blocked, while the three optocouplers on the left are normally open, and electrodes 1, 2, and 4 are connected to the peripheral circuit. In transcutaneous electrical stimulation (TES) mode, the three optocouplers on the left are blocked, while the optocouplers inside the H-bridge on the right are switched sequentially, and electrodes 3 and 4 are connected to the peripheral circuit. Since the peripheral circuit on the left operates at a low voltage of 3.3V or below, while the peripheral circuit on the right operates at a high voltage of 40V or below, adding optocouplers to the electrodes prevents short circuits between the high and low voltages on the skin surface, providing protection.

[0041] Figure 3A 3D exploded view of the entire fabric electronics system is shown. From bottom to top, the components are: hydrogel 31, medical double-sided tape 32, bottom fabric circuit and electrode array 33, fabric substrate 34, top fabric circuit 35, and patch electronic components 36. The medical double-sided tape 32 is laser-cut to a specific shape, and the hydrogel 31 is obtained by dripping a precursor solution into the groove formed by the medical double-sided tape 32 and curing it with ultraviolet light.

[0042] Figure 4 The image shows a physical example of the fabric electronic system and its effect when worn on the biceps of the arm. It is evident that the electronic system has good flexibility and high space utilization.

[0043] Figure 5 The program logic diagram of the fabric electronics system in both transcutaneous electrical stimulation (TES) and electromyography (EMG) detection modes is shown. TES is controlled by a 20ms timer interrupt, which determines whether to proceed to the next cycle at the end of the interrupt. This process first triggers DMA channel 1, causing the ADC to sample the upcoming electrical stimulation (pulse duration ~3ms), and immediately generate positive and negative electrical stimulation waveforms. No sampling occurs during the remaining 17ms of the cycle, thus reducing storage space and transmission bandwidth usage. After DMA channel 1 completes one round of sampling, DMA channel 2 is immediately triggered, transmitting the acquired electrical stimulation waveform to the Bluetooth module, and finally to the host computer via Bluetooth. EMG detection is completed through a loop execution of DMA channel 1 and DMA channel 2. This process first triggers DMA channel 1, causing the ADC to sample the EMG signal. After the ADC conversion is complete, DMA channel 2 is immediately triggered, simultaneously performing the next round of EMG signal sampling. DMA channel 2 transmits the acquired EMG signal to the Bluetooth module, and finally to the host computer via Bluetooth. The use of DMA in both modes enables the fabric electronic system to simultaneously acquire and transmit signals, greatly improving data transmission efficiency and real-time performance.

[0044] Figure 6 The functional block diagram of the fabric electronic system is shown. In electromyography (EMG) detection mode, the EMG signals detected by the three electrodes (electrodes 1, 2, and 4) are processed by an analog front-end and bandpass filtering, then acquired by the microcontroller's 12-bit ADC channel, and finally transmitted to the host computer via Bluetooth. In transcutaneous electrical stimulation (TES) mode, an electrical stimulation current is output through a current source powered by a 3.7V lithium battery boosted to 40V. The amplitude of the electrical stimulation current is controlled by the microcontroller's DAC, and the direction of the electrical stimulation current is controlled by an H-bridge. The electrical stimulation current detected by the three electrodes (electrodes 1, 2, and 4) is processed by an analog front-end and bandpass filtering, then acquired at high rate by the microcontroller's 12-bit ADC channel during the electrical stimulation pulse time, and finally transmitted to the host computer via Bluetooth.

[0045] Figure 7 The electrical stimulation waveforms generated by the fabric electronic system and the detected electromyographic signals are shown. Figure 7 The electrical stimulation pulses of type a are bipolar and electrically neutral, preventing charge accumulation on the skin and enhancing the comfort and safety of transcutaneous electrical stimulation. The corresponding voltage is as follows: Figure 7 As shown in b. Figure 7 c represents the electromyographic signal acquired during biceps brachii contraction, which has a high signal-to-noise ratio and a normal power spectral density distribution. Figure 7 d).

[0046] Figure 8 The comparison between this fabric-based electronic system and a commercially available PCB with similar functionality is shown. Figure 8 a represents the current consumption of both in idle mode, when detecting electromyographic signals (EMG), and when applying electrical stimulation (EMC), respectively. Figure 8 b, Figure 8 c represents the voltage waveforms applied across a 1kΩ resistor to the fabric electronics system and a commercial PCB board, respectively. Similar current consumption and nearly identical EMS waveforms demonstrate the reliability of the fabric electronics system.

[0047] Figure 9 This demonstrated the fabric electronic system's ability to detect muscle fatigue. The system was worn on a volunteer's biceps and a 5 kg weight was applied for 2.5 minutes. Figure 9 a represents the electromyographic signal collected during the aforementioned load process. Figure 9 b、 Figure 9 c represents the root-mean-square amplitude and short-time Fourier transform spectrum of the electromyographic (EMG) signal, respectively. The increase in the root-mean-square amplitude of the EMG signal over time is due to enhanced nerve recruitment caused by gradual muscle fatigue. The frequency distribution of the short-time Fourier transform spectrum of the EMG signal shifts to lower frequencies over time due to the decrease in action potential conduction velocity caused by gradual muscle fatigue. This demonstrates the ability of the fabric electronic system to detect muscle fatigue.

[0048] Figure 10 This demonstrated the fabric's electronic system's ability to treat muscle fatigue. Volunteers' biceps were used in the exercise. Figure 9 The corresponding weight-bearing experiment was conducted to induce muscle fatigue, followed by 10 seconds of electrical stimulation therapy using the fabric's electronic system. As a comparison, the volunteer underwent the weight-bearing experiment again two days later, followed by 10 seconds of rest. The median frequency (MDF) of the electromyographic signals throughout the experiment is shown below. Figure 10As shown, the lower the MDF value, the higher the degree of muscle fatigue. During a 10-second resting period, the MDF value recovered by only 11%, compared to nearly 65% ​​after 10 seconds of transcutaneous electrical stimulation. This demonstrates the potential of this fabric electronics system to accelerate the recovery of muscle bioelectrical activity.

[0049] To further verify the effectiveness of this fabric-based electronic system in treating muscle fatigue, maximal voluntary contractile force (MVC) was used to quantify muscle fatigue: a lower MVC value indicated higher muscle fatigue. The MVC measurement was performed as follows: the biceps brachii was pulled through a cable and pulley force sensor for 3 seconds, and the maximum reading of the force sensor was taken as the MVC. Subsequently, a volunteer (with an initial biceps MVC of 170N) continuously pulled through the force sensor using the same device. When the sensor reading remained below 100N for 5 consecutive seconds, the biceps brachii was considered to be at exhaustion. After exhaustion, the volunteer underwent either quiet rest or transcutaneous electrical stimulation to relieve muscle fatigue, and the MVC value was measured every minute. Figure 11 As shown, after applying transcutaneous electrical stimulation, the muscle volume (MVC) recovered to 98% of its initial state within 4 minutes, compared to only 89% in the resting control group. This demonstrates that the fabric electronic system of the present invention can accelerate muscle strength recovery.

Claims

1. A fabric electronic system integrating muscle fatigue detection and treatment, characterized in that, The application relates to a kind of wearable devices, which are integrated with conductive fabric lines and physiological electrodes, vertical interconnection via and patch components on the same fabric substrate, and are provided with conductive fabric lines on both sides of the fabric substrate and connected with each other through vertical interconnection via, the overall formed circuit includes electrode array, signal conditioning circuit, wherein the electrode array is used for detecting electromyographic signals and applying transcutaneous electrical stimulation, the signal conditioning circuit is used for electromyographic signal amplification, electrical stimulation waveform conditioning and overall timing logic control, and has the functions of safety isolation and electrical stimulation waveform detection. The vertical interconnection via is formed by brushing conductive paste on both sides of the required position by air pressure perfusion method, and the conductive paste is made to penetrate into the texture structure of the fabric substrate in the position by air blowing on both sides through an air gun, so that the corresponding areas of the fabric substrate realize front and back surface communication, wherein the conductive paste is intermetallic compound LM / Cu NP paste formed by mixing liquid metal and copper nanoparticles by a centrifugal mixer or a high-speed defoaming machine.

2. The muscle fatigue detection and treatment integrated fabric electronics system of claim 1, wherein, The electrode array is constructed by adopting single-pair electrode multiplexing, and the electrode array includes electrodes No.1 to No.4, wherein electrode No.1 and electrode No.2 are positive and negative input terminals of electromyographic signals, electrode No.3 is a positive output terminal of electrical stimulation, and electrode No.4 is simultaneously used as a negative output terminal of electrical stimulation and an output terminal of a right leg driving circuit; wherein the electrode for signal sampling is separated from the electrode for applying electrical stimulation, so as to avoid the signal sampling from being affected by electrode polarization.

3. The muscle fatigue detection and treatment integrated fabric electronics system of claim 2, wherein, Three independent optocoupler isolators and an H-bridge circuit composed of four optocoupler isolators are used in the signal conditioning circuit, wherein electrode No.1, electrode No.2 and electrode No.4 are connected to the peripheral circuit through an independent optocoupler isolator respectively, electrode No.3 and electrode No.4 are connected to the peripheral circuit through the H-bridge circuit, and the four electrodes are selectively connected to the circuit by controlling the optocoupler isolators, so as to effectively realize independent switching of electromyographic detection and electrical stimulation application, avoid signal interference and ensure system safety.

4. The muscle fatigue detection and treatment integrated fabric electronics system of claim 3, wherein, A constant current source is used to output stimulation current in the signal conditioning circuit, the amplitude of the stimulation current is controlled by a digital-to-analog converter of a microcontroller, the direction of the stimulation current is controlled by an H-bridge circuit of a load end of the constant current source, the duty ratio, frequency and amplitude of the stimulation current are real-time adjustable, the output current is ensured to be neutral, and the harm of excessive current to the skin and tissues is avoided.

5. The muscle fatigue detection and treatment integrated fabric electronics system of claim 3, wherein, In the electrical stimulation application mode, the independent optocoupler isolators connected to electrode No.1, electrode No.2 and electrode No.4 are all blocked, and the optocoupler isolators in the H-bridge circuit are sequentially switched on; in the electromyographic detection mode, the optocoupler isolators in the H-bridge circuit are blocked, and the independent optocoupler isolators connected to electrode No.1, electrode No.2 and electrode No.4 are all always on.

6. The muscle fatigue detection and treatment integrated fabric electronics system of claim 1, wherein, The conductive fabric lines and physiological electrodes are formed by cutting conductive fabric according to a pre-designed pattern by laser, and then the conductive fabric lines and physiological electrodes are transferred to both sides of the fabric substrate by transfer printing, and the conductive fabric lines and physiological electrodes on both sides are connected through the vertical interconnection via.

7. The muscle fatigue detection and treatment integrated fabric electronics system of claim 1, wherein, The patch components are welded on the conductive fabric lines by solder paste to form a complete circuit.

8. The muscle fatigue detection and treatment integrated fabric electronics system of claim 1, wherein, The lower side surface of the fabric substrate is provided with conductive fabric lines and a physiological electrode layer in sequence, and a medical double-sided adhesive tape and a hydrogel layer; the medical double-sided adhesive tape and the hydrogel layer are formed by laser cutting the medical double-sided adhesive tape to form recesses with the same shape as the physiological electrodes, and injecting a hydrogel precursor liquid into the recesses and curing by ultraviolet light. The upper side surface of the fabric substrate is provided with conductive fabric lines and patch electronic devices.

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