Device and method for collecting and processing electromyographic signals

Abstract

The present application provides a device for collecting and processing human electromyographic signals, the device comprising: an electrode module configured to collect human electromyographic signals; the electrode module comprising a base structure and at least two electrodes, the at least two electrodes being arranged at intervals and disposed on the surface of the base structure.

Description

Technical Field

[0001] The present application relates to the field of signal acquisition and processing, and in particular to a device and method for acquiring and processing electromyographic signals. Background Art

[0002] As people pay more attention to scientific exercise and physical health, smart wearable devices are developing greatly. The guidance and monitoring of smart wearable devices rely on sensors and electrodes. At present, smart wearable devices face the contradiction between comfort and signal quality (stability and signal-to-noise ratio). Common practices include but are not limited to the use of hydrogel electrodes, skin surface treatment, dry electrode materials and colloid material fixation. These methods can help improve the quality of the collected signals, but they face at least one of the problems of poor comfort, short service life and complex operation. Although the direct use of dry electrodes (metal fabric electrodes, conductive silicon electrodes, etc.) can solve the above-mentioned problems, the electrode module and human skin are prone to the problem of not fitting, which may lead to the inability to collect signals and increase noise; in addition, when the human body moves, the contact position between the electrode and the human body may move relative to each other. The movement of the electrode will result in the failure to collect the target position signal, affecting the signal quality and increasing noise; finally, the dry electrode has a large contact impedance with the human skin, which is more likely to cause large fluctuations and affect the signal quality.

[0003] Therefore, the present application provides a device for collecting and processing human electromyographic signals, which can significantly improve the quality of electromyographic signals at the human skin collected by the electrode module while ensuring comfort. Summary of the invention

[0004] One of the embodiments of the present application provides a device for collecting and processing human electromyographic signals, the device comprising: an electrode module configured to collect human electromyographic signals; the electrode module comprising a base structure and at least two electrodes, the at least two electrodes being arranged at intervals and disposed on the surface of the base structure.

[0005] In some embodiments, the at least two electrodes include a first electrode and a second electrode, and the first electrode and the second electrode are arranged side by side and disposed on a surface of the base structure.

[0006] In some embodiments, the at least two electrodes further include a reference electrode, and the first electrode, the reference electrode and the second electrode are sequentially arranged in parallel and disposed on the surface of the base structure.

[0007] In some embodiments, the at least two electrodes further include a third electrode and a fourth electrode, and the third electrode and the fourth electrode are arranged side by side and disposed on the surface of the base structure; wherein the first electrode and the third electrode are disposed side by side, and the second electrode and the fourth electrode are disposed side by side.

[0008] In some embodiments, the electrode module includes a plurality of protrusion structures, and the plurality of protrusion structures are located on the surface of the at least two electrodes or the base structure.

[0009] In some embodiments, the protrusion structures are arranged in an array or randomly distributed on the surface of the at least two electrodes or the base structure.

[0010] In some embodiments, the protruding structure is hollow inside, and the hollow part of the protruding structure has a filler.

[0011] In some embodiments, the height of the protruding structure is 0.5 mm to 10 mm.

[0012] In some embodiments, the electrode module comprises a plurality of suction cup structures, and the plurality of suction cup structures are located on the surface of the at least two electrodes or the base structure.

[0013] In some embodiments, the plurality of suction cup structures are arranged in an array or randomly distributed on the at least two electrodes or on the surface of the base structure.

[0014] In some embodiments, the plurality of suction cup structures are distributed on the surface of the base structure around the at least two electrodes.

[0015] In some embodiments, the suction cup structure is a three-dimensional structure, and the suction cup structure includes a hollow portion, and the hollow portion has an opening at an end of one end of the suction cup structure for contacting human skin.

[0016] In some embodiments, the suction cup structure further includes an intermediate structure, wherein the intermediate structure is located in a hollow portion of the suction cup structure, wherein a portion of the intermediate structure is connected to a side wall of the suction cup structure where the hollow portion is located.

[0017] In some embodiments, the intermediate structure divides the hollow portion of the suction cup structure into a plurality of interconnected spatial regions.

[0018] In some embodiments, the electrode module may further include a plurality of bump structures, and the bump structures are located on the surface of the substrate structure or the at least two electrodes.

[0019] In some embodiments, the height of the plurality of bump structures is 10 μm to 80 μm.

[0020] In some embodiments, the distribution density of the plurality of bump structures may be 2 / 2.25 mm2 to 10 / 2.25 mm2.

[0021] In some embodiments, the electrode module further includes a plurality of air holes, and the plurality of air holes are located on the electrode and / or the base structure.

[0022] An embodiment of the present application provides a wearable device, which includes a top garment and a pair of trousers, wherein the top garment and the trousers at least include an electromyographic module for collecting electromyographic signals of a human body.

[0023] In some embodiments, the upper garment includes at least: at least one upper garment sensor module, configured to collect upper body motion data of the human body; at least one upper garment data processing module, configured to receive and process the upper body motion data of the human body; and an upper garment base, configured to carry the at least one upper garment sensor module and the at least one upper garment data processing module.

[0024] In some embodiments, the at least one upper garment sensor module includes at least a first upper garment sensor module and a second upper garment sensor module, wherein the first upper garment sensor module is located on a left side of the upper garment base, and the second upper garment sensor module is located on a right side of the upper garment base.

[0025] In some embodiments, the first upper garment sensor module and the second upper garment sensor module include at least the electromyographic module, the electrocardiographic sensor, the respiratory sensor, the temperature sensor, the humidity sensor, the inertial sensor, the acid-base sensor, and the sound wave transducer.

[0026] In some embodiments, the inertial sensor is located in the garment processing module.

[0027] In some embodiments, the at least one top processing module includes at least a first top processing module and a second top processing module; wherein the first top processing module is located at the left shoulder position of the top garment base, and the first top processing module is communicatively connected to the first top sensor module; the second top processing module is located at the right shoulder position of the top garment base, and the second top processing module is communicatively connected to the second top sensor module.

[0028] In some embodiments, the first upper garment processing module and the second upper garment processing module are in a master-slave relationship or a parallel relationship.

[0029] In some embodiments, the pants garment includes at least: at least one pants sensor module, configured to collect human lower body movement data; at least one pants data processing module, configured to receive and process the human lower body movement data; and a pants garment base, configured to carry the at least one pants sensor module and the at least one pants data processing module.

[0030] In some embodiments, the at least one trousers sensor module includes at least a first trousers sensor module and a second trousers sensor module, wherein the first trousers sensor module is located on a left side of the trousers garment base and the second trousers sensor module is located on a right side of the trousers garment base.

[0031] In some embodiments, the first pants sensor module and the second pants sensor module include at least the electromyography module, the electrocardiogram sensor, the breathing sensor, the temperature sensor, the humidity sensor, the inertial sensor, the acid-base sensor, and the sound wave transducer.

[0032] In some embodiments, the at least one trouser processing module includes at least a first trouser processor module and a second trouser processing module; wherein the first trouser processing module is located on the left side of the left leg of the trouser garment base, and the first trouser processing module is communicatively connected to the first trouser sensor module; the second trouser processing module is located on the right side of the right leg of the trouser garment base, and the second trouser processing module is communicatively connected to the second trouser sensor module.

[0033] In some embodiments, the first trousers processing module and the second trousers processing module are in a master-slave relationship or a parallel relationship. BRIEF DESCRIPTION OF THE DRAWINGS

[0034] The present application will be further described in the form of exemplary embodiments, which will be described in detail by way of the accompanying drawings. These embodiments are not restrictive, and in these embodiments, the same number represents the same structure, wherein:

[0035] Figure 1 is a schematic diagram of the structure of an electrode module according to some embodiments of the present application;

[0036] Figure 2 is a schematic structural diagram of another electrode module according to some embodiments of the present application;

[0037] Figure 3 is a structural schematic diagram of another electrode module according to some embodiments of the present application;

[0038] Figure 4 It is an electrode impedance parallel model shown in some embodiments of the present application;

[0039] Figure 5 It is an electrode impedance parallel model of a conductive silicon electrode according to some embodiments of the present application;

[0040] Figure 6 is a graph showing the relationship between a conductive silicon electrode and its thickness according to some embodiments of the present application;

[0041] Fig. 7A is a schematic diagram of the structure of electrodes according to some embodiments of the present application;

[0042] Figure 7B It is a parallel model of metal fabric conductive silicon composite material electrodes according to some embodiments of the present application;

[0043] Figure 8 is a schematic structural diagram of a suction cup structure according to some embodiments of the present application;

[0044] Fig. 9 is a cross-sectional view of another suction cup structure according to some embodiments of the present application;

[0045] Fig.10 is a cross-sectional view of another suction cup structure according to some embodiments of the present application;

[0046] Fig.11 is a cross-sectional view of another suction cup structure according to some embodiments of the present application;

[0047] Fig.12 is a schematic structural diagram of an electrode module with a suction cup structure according to some embodiments of the present application;

[0048] Fig.13 is a schematic structural diagram of another electrode module with a suction cup structure according to some embodiments of the present application;

[0049] Fig.14 is a schematic diagram of an exemplary structure of a wearable device according to some embodiments of the present application;

[0050] Fig.15 is an exemplary structural diagram of a wiring connection method of a top wearable device according to some embodiments of the present application;

[0051] Fig.16A is an exemplary structural diagram of the elastic design of the underarm position of the upper wearable device according to some embodiments of the present application;

[0052] Fig. 16B is an exemplary structural diagram of the elastic design of the upper arm position of the upper wearable device shown in some embodiments of the present application;

[0053] Fig.17A is an exemplary structural diagram of a ring-shaped elastic design of an electrode module of a top wearable device according to some embodiments of the present application;

[0054] Fig. 17B is an exemplary structural diagram of a specific direction elastic design of an electrode module of a wearable upper garment device according to some embodiments of the present application;

[0055] Fig.18 is an exemplary structural diagram of a hollow design of a wearable device according to some embodiments of the present application;

[0056] Fig.19A is an exemplary structural diagram of a knife-shaped electrode module according to some embodiments of the present application; and

[0057] Fig.19B It is an exemplary cross-sectional view of a knife-shaped electrode module according to some embodiments of the present application. DETAILED DESCRIPTION

[0058] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following is a brief introduction to the drawings required for use in the description of the embodiments. Obviously, the drawings described below are only some examples or embodiments of the present application. For ordinary technicians in this field, the present application can also be applied to other similar scenarios based on these drawings without creative work. Unless it is obvious from the language environment or otherwise explained, the same reference numerals in the figures represent the same structure or operation.

[0059] It should be understood that the "system", "device", "unit" and / or "module" used herein are a method for distinguishing different components, elements, parts, portions or assemblies at different levels. However, if other words can achieve the same purpose, the words can be replaced by other expressions.

[0060] As shown in this application and claims, unless the context clearly indicates an exception, the words "a", "an", "an" and / or "the" do not refer to the singular and may also include the plural. Generally speaking, the terms "comprises" and "includes" only indicate the inclusion of the steps and elements that have been clearly identified, and these steps and elements do not constitute an exclusive list. The method or device may also include other steps or elements.

[0061] Flowcharts are used in the present application to illustrate the operations performed by the system according to the embodiments of the present application. It should be understood that the preceding or following operations are not necessarily performed accurately in order. On the contrary, the various steps may be processed in reverse order or simultaneously. At the same time, other operations may also be added to these processes, or one or more operations may be removed from these processes.

[0062] With people's attention to scientific exercise and physical health, smart wearable devices are developing greatly. Among them, smart wearable devices that collect bioelectric signals mainly rely on electrodes. Specifically, electromyographic signals, as a type of bioelectric signal, are the source of electrical signals that generate muscle power. It is the superposition of action potentials of many motor units in the muscle in time and space, and largely reflects the movement state of nerves and muscles. From the perspective of electromyographic signal collection methods, there are generally two types. One is to collect through needle electrodes inserted into the muscle, that is, needle electromyographic signals. Its advantages are small interference and easy identification, but it will cause harm to the human body; the other is to collect electromyographic signals on the surface of the human skin by sticking electrode sheets on the human skin, that is, surface electromyographic signals (SEMG). This method is generally limited to collection when the human body is stationary. When the human body moves, the electrode and the human body move relative to each other, and the collected electromyographic signals are inaccurate. At present, commonly used practices include but are not limited to the use of hydrogel electrodes, skin surface treatment, dry electrode materials and colloid material fixation. These methods can help improve the quality of the collected signals, but face at least one of the problems of poor comfort, short service life, and complex operation.

[0063] The electrode module and intelligent wearable device (for example, clothing, wristband, shoulder strap, etc.) described in the embodiment of the present application mainly involve the collection of skin surface electromyographic signals (hereinafter collectively referred to as electromyographic signals), which can be obtained from many parts of the human body, such as calves, thighs, buttocks, waist, back, chest, shoulders, neck, etc. The electromyographic signals obtained from different parts carry the motion and functional information of the corresponding parts. For example, the electromyographic signals on the legs reflect the posture and motion state of the legs, such as walking, running, squatting, etc. Therefore, electromyographic signals can be collected by intelligent wearable devices to meet people's requirements for sports and fitness guidance. In order to collect the electromyographic signals of the user's body in all directions when the user is exercising, the intelligent wearable device can be clothing. By setting electrode modules corresponding to various parts of the human body (for example, calves, thighs, buttocks, waist, back, chest, shoulders, neck, etc.) in the clothing, the electromyographic signals of various parts of the user's body when exercising can be collected. Optionally, the smart wearable device can directly analyze and process the collected electromyographic signals, or transmit the collected electromyographic signals to a processing terminal (e.g., a mobile terminal device, a cloud server) by wired or wireless means for analysis and processing to determine whether the user's movement is correct, and provide corresponding feedback to the user to correct the user's incorrect movement. Furthermore, the smart wearable device can also formulate a scientific personal exercise plan for the user based on the collected electromyographic signals and guide the user to exercise. In addition, the use of electromyographic signals to study the state of human movement is also of great value. For example, in medical rehabilitation engineering, electromyographic signals can be used for patient treatment, and in bionics, electromyographic signals can be used for the study of artificial prostheses.

[0064] When clothing is used as a smart wearable device to collect electromyographic signals of the user during exercise, the electrode module must not only be able to collect electromyographic signals of good quality, but also have characteristics such as softness, ultra-thinness, tolerance, and skin-friendliness to avoid discomfort caused by the electrodes to the user when the user wears the clothing for exercise and fitness.

[0065] In some embodiments, the amplitude of the original electromyographic signal directly collected by the electrode is very small and contains a large amount of noise, and filtering, differential amplification and other processing are required before subsequent analysis or processing of the electromyographic signal can be performed.

[0066] In some embodiments, the noise in the original electromyographic signal mainly includes common mode noise, and the common mode noise is mainly caused by the power frequency common mode signal. Therefore, in order to reduce the common mode noise, the power frequency common mode signal can be effectively suppressed by a differential circuit, a right leg drive circuit, a filter circuit, etc., so as to reduce or eliminate the common mode noise. Preferably, a differential circuit and a right leg drive circuit can be used to effectively suppress the power frequency common mode signal. In some embodiments, considering that the common mode noise is mainly caused by the power frequency, the frequency of the common mode noise is mainly concentrated near 50Hz or 60Hz (or its harmonics), and the frequency distribution of the main intensity of the electromyographic signal is 20 to 140Hz, so the common mode noise can be filtered out by one or more filters or traps. For example, in some embodiments, a 50Hz trap and a 140Hz low-pass filter can be used to filter out the common mode noise. For another example, a 50Hz trap, a 100Hz trap, a 150Hz trap and a 240Hz low-pass filter can be used to filter out the common mode noise. For another example, a 50 Hz notch filter, a 150 Hz notch filter, and a 230 Hz low-pass filter may be used to filter out common mode noise.

[0067] In some embodiments, the noise in the original electromyographic signal may also include differential mode noise caused by the conversion of the common mode signal to the differential mode signal. For example, when a differential circuit is used to suppress common mode noise, the fluctuation of the contact impedance between the electrode and the skin may cause the contact impedance between the two electrodes corresponding to the differential circuit and the human skin to be inconsistent, thereby converting the common mode signal into a differential mode signal and causing differential mode noise, especially the differential amplifier circuit may amplify the differential mode signal. Therefore, the amount of the common mode signal converted into the differential mode signal may be reduced by reducing or avoiding the contact impedance fluctuation. For example, the differential mode noise caused by the contact impedance fluctuation may be reduced by reducing the value of the contact impedance between the electrode and the skin so that the contact impedance has a smaller fluctuation range.

[0068] In some embodiments, the contact impedance fluctuation causes the two electrodes corresponding to the differential circuit to have inconsistent contact impedance with the skin, which can also cause a voltage division problem, making the amplitude of the collected electromyographic signal small and not strong enough. Therefore, the voltage division problem can be solved by increasing the input impedance of the circuit connected to the electrode (e.g., the differential circuit). When the difference between the input impedance and the contact impedance is large enough, the influence of the contact impedance fluctuation on the electromyographic signal strength can be reduced or avoided.

[0069] In some embodiments, by reducing the contact impedance, noise can be reduced to improve the quality of the electromyographic signal. In some embodiments, the quality of the electromyographic signal can also be graded so that the electromyographic signals of poor quality can be eliminated and the high-quality electromyographic signals can be retained, or the electromyographic signals of poor quality can be processed into high-quality electromyographic signals by an algorithm. Specifically, a contact impedance evaluation circuit can be designed to be connected to the electrode. The contact impedance evaluation circuit can be used to measure the size of the electrode contact impedance or whether it is abnormal. The size of the electrode contact impedance or whether it is abnormal will directly affect the quality of the collected electromyographic signal. Therefore, the coefficient used to measure the contact impedance can be used as an indicator of the quality of the electromyographic signal collection, and this indicator is used to give the collected electromyographic signal a weight. The greater the weight, the higher the quality of the electromyographic signal.

[0070] In some embodiments, in order to more accurately measure the electromyographic signals of various parts of the human body, different numbers of electrodes can be arranged correspondingly in various parts of the human body when collecting the electromyographic signals of various parts of the human body. For example, multiple electrodes used to collect the electromyographic signals of a certain part can be integrated into an electrode module. The electrode module can be arranged in the central area of ​​the muscle of the part and include at least two electrodes. The at least two electrodes can be arranged in sequence along the length direction of the muscle fibers of the part.

[0071] Figure 1 is a schematic diagram of the structure of the electrode module according to some embodiments of the present application. Figure 1 As shown, the electrode module 100 may include a base structure 103 and two electrodes (also referred to as electrode units). The two electrodes are spaced apart and distributed on the surface of the base structure 103. In some embodiments, the base structure 103 may be made of a flexible insulating material (e.g., resin, soft PVC, silicone), and may be rectangular, circular, or other irregular shapes. The electrodes may be fixedly connected to the base structure 103 by pasting, clamping, welding, etc., and the electrode module 100 may be fixed to the corresponding position of the wearable device through the base structure 103. Specifically, in some embodiments, the two electrodes may include a first electrode 101 and a second electrode 102. When the electrode module 100 is used to collect electromyographic signals, the first electrode 101 and the second electrode 102 may be arranged along the length direction of the muscle fibers ( Figure 1The electrode module 102 is arranged in sequence along the x direction in the muscle fiber length direction. Different positions along the length direction of the muscle fiber have different electric potentials. The position of the muscle fiber where the first electrode 101 is located has a first electric potential, and the position of the muscle fiber where the second electrode 102 is located has a second electric potential. There is a potential difference between the first potential and the second potential (the potential difference can be used to reflect the electromyographic signal). In some embodiments, the electrode module may also include a differential circuit, and the first electrode and the second electrode may be electrically connected to two input terminals of the differential circuit, respectively. The differential circuit may refer to a circuit structure that amplifies differential mode signals and suppresses common mode signals.

[0072] Figure 2 is a schematic diagram of the structure of another electrode module according to some embodiments of the present application. Figure 2As shown, the electrode module 200 may include a first electrode 201, a third electrode 204, and a second electrode 202 arranged at intervals on the surface of the base structure 203 along the length direction of the muscle fiber. Among them, the position of the muscle fiber where the first electrode 201 is located has a first potential, the position of the muscle fiber where the second electrode 202 is located has a second potential, and the position of the muscle fiber where the third electrode 204 is located has a third potential. Further, there is a potential difference between the first potential and the second potential, and the first electrode 201 and the second electrode 202 are respectively connected to the input end of the differential circuit, and the third electrode 204 in the middle can be used as a reference electrode to record the MA (motion artifacts) noise and the noise caused by poor contact in the electromyographic signal collected by the electrode module, thereby weakening it to a certain extent. Here, MA refers to noise caused by movement, such as movement causing changes in electrode fit or position, resulting in increased noise in the output signal. In some embodiments, the MA noise frequency has a certain relationship with movement and can be filtered out by a high-pass filter. However, in some cases, MA noise can cause a multiplication effect with other sources to cause the superposition of frequencies, and it is difficult to filter out MA noise through a filter. In order to better deal with the problem of MA noise, in some embodiments, a third electrode 204 can be set between the first electrode 201 and the second electrode 202. First, the third electrode 204 is located between the first electrode 201 and the second electrode 202. The third electrode 204 has a reference meaning representing the electrode module 200. It can be measured separately to obtain relevant information of the third electrode 204, such as contact impedance, power frequency output, etc. The relevant information of the third electrode 204 can be introduced into the evaluation system as a quality supervision value for judging the electrode module 200 to collect electromyographic signals. Secondly, the third electrode 204 is located between the first electrode 201 and the second electrode 202, and the third electrode 204 will change with the state change of the entire electrode module 200. For example, when the first electrode 201 and the second electrode 202 introduce MA noise or other noise introduced by the electrode not fitting with the skin when measuring the electromyographic signal, it will also be reflected on the third electrode 204. As an exemplary illustration only, when the electrode module 200 only includes the first electrode 201 and the second electrode 202. The reference ground in the measurement circuit of the electrode module 200 is connected to the first electrode 201 or the second electrode 202 or a fixed source. The result measured by the electrode module is actually a differential amplification of the difference between the first electrode 201 and the second electrode 202 .When the electrode module 200 is provided with the third electrode 204, the reference ground is connected to the third electrode 204. The result of the electrode module measurement is to differentially amplify the difference between the potential difference between the first electrode 201 and the third electrode 204 and the potential difference between the second electrode 204 and the third electrode. The potential measured by the third electrode 204 includes noise caused by MA and poor contact. The noise caused by MA and poor contact can be effectively reduced by measuring the potential difference between the first electrode 201 and the third electrode 204 and the potential difference between the second electrode 204 and the third electrode. Again, the third electrode 204 can be used as the output end of the right leg drive circuit. The right leg drive circuit collects the common mode signal of the electrode module, and after directional amplification, it is fed back to the human body through the third electrode 204, which can effectively suppress the common mode signal from the source. In addition, the third electrode 204 can be used as an electromyographic signal acquisition electrode similar to the first electrode 201 and the second electrode 202, which can help realize the acquisition combination of different electrode pairs. For example, the first electrode 201 and the third electrode 204 can collect a group of electromyographic signals, and the second electrode 202 and the third electrode 204 can collect another group of electromyographic signals. The electromyographic signals are extracted through the properties of these two groups of electromyographic signals (for example, within a certain range, the electromyographic signal strength is proportional to the spacing between the acquisition electrodes) to optimize the signal-to-noise ratio. In some embodiments, the base structure 203 is the same as or similar to the base structure 103.

[0073] Figure 3 is a schematic diagram of the structure of another electrode module according to some embodiments of the present application. Figure 3As shown, the electrode module 300 may include two groups of electrodes, and the two groups of electrodes are arranged on the surface of the base structure 303 at intervals along the width direction (y direction) of the muscle fiber, and the two electrodes in each group of electrodes are arranged at intervals along the length direction of the muscle fiber. Specifically, the two groups of electrodes are respectively a first group of electrodes 310 and a second group of electrodes 320, the first group of electrodes 310 includes a first electrode 301 and a second electrode 302, and the second group of electrodes 320 includes a third electrode 304 and a fourth electrode 305. The position of the muscle fiber where the first electrode 301 is located has a first potential, the position of the muscle fiber where the second electrode 302 is located has a second potential, the position of the muscle fiber where the third electrode 304 is located has a third potential, and the position of the muscle fiber where the fourth electrode 305 is located has a fourth potential. In some embodiments, the first electrode 301 and the third electrode 304 are connected to one input end of the differential circuit together, and the larger, smaller, or average of the first potential and the third potential can be used as the input of the input end, while the second electrode 302 and the fourth electrode 302 are connected to the other input end of the differential circuit, and the larger, smaller, or average of the second potential and the fourth potential can be used as the input of the other input end of the differential circuit. Based on the input of the two input ends of the differential circuit, the electromyographic signal of the position where the electrode module 300 is located can be obtained. In other embodiments, the first electrode 301 and the second electrode 302 can be connected to the two input ends of the differential circuit respectively, and the third electrode 304 and the fourth electrode 305 can be connected to the two input ends of another differential circuit respectively. At this time, there is a first potential difference (i.e., a first differential signal or a first electromyographic signal) between the first potential and the second potential, and there is a second potential difference (i.e., a second differential signal or a second electromyographic signal) between the third potential and the fourth potential. Based on the first electromyographic signal and the second electromyographic signal, the electromyographic crosstalk influence information near the muscle fibers in the Y direction can be obtained, so that based on the muscle crosstalk influence information, the electromyographic signal interference of the muscles near the part to be collected can be eliminated through an algorithm, so as to collect more accurate electromyographic signals. In this embodiment, the combination of electromyographic signals at multiple positions of the human body part corresponding to the electrode module can be extracted through two groups of electrodes, so as to extract more accurate electromyographic signals.

[0074] It should be noted that the above embodiments are only exemplary, and the number and distribution of electrodes in the electrode module are not limited to Figure 1 , Figure 2 and Figure 3 As long as at least two of the multiple electrodes in the electrode module are arranged at intervals along the length direction of the muscle fibers, no further details will be given here.

[0075] When at least two electrodes (for example, the first electrode and the second electrode) of the electrode module are attached to the skin for electromyographic signal collection, contact impedance is formed when each electrode contacts the skin. When the human body moves, the pressure, position, etc. of the electrode and the skin will change to a certain extent, causing the contact impedance to fluctuate, thereby affecting the accuracy of the electromyographic signal. In some embodiments, in order to reduce the differential mode signal noise caused by the large difference in contact impedance formed when at least two electrodes (for example, the first electrode and the second electrode) in the electrode module are attached to the human skin, it can be achieved by reducing the contact impedance fluctuation. Specifically, the contact impedance between at least two electrodes and the skin can be reduced so that the contact impedance does not fluctuate within a large range, thereby making the difference in contact impedance at both ends of the electrode small or consistent.

[0076] For ease of understanding and explanation, when the electrode is attached to the skin for myoelectric signal collection, the contact between the electrode and the skin can be equivalent to the parallel connection of a capacitor and a resistor, and the contact impedance can be calculated by formula (1):

[0077]

[0078] Among them, |z| is the contact impedance, S is the contact area between the electrode and the skin, d is the distance between the electrode and the skin, ρ and ε represent the average resistivity and capacitance dielectric constant between the electrode and the skin, respectively, ω = 2π·f, and f is the frequency of the electromyographic signal. From formula (1), it can be concluded that the larger the electrode area and the smaller the distance between the electrode and the skin, the more conducive to reducing the contact impedance between the electrode and the skin.

[0079] Furthermore, in order to make the contact impedance between the electrode and the skin smaller, the contact area between the electrode and the skin can be increased as much as possible. Therefore, the contact area between the electrode and the skin can be ensured to be larger by designing the shape and size of the surface where the electrode contacts the skin. In some embodiments, the shape of the surface where the electrode contacts the skin can be rectangular, wherein the length of the surface of the electrode used to contact the skin can be 1cm to 10cm, and the width can be 1cm to 4cm. For example, the size of the surface can be 4cm×2cm, or 3cm×1.5cm, or 2cm×1cm. In some embodiments, the shape of the electrode can also be other regular or irregular shapes such as circular, triangular, hexagonal, etc. In practical applications, the shape of the electrode can depend on the shape of the muscle at the site where the electromyographic signal is to be collected.

[0080] It should be noted that the surface size of the electrode used to contact the skin is not limited to the above-mentioned size, but can also be larger or smaller, which can be determined specifically according to the measurement part. For example, the size and distribution of the electrode will be limited by the muscle size and intermuscular crosstalk. In some embodiments, the electrodes can be distributed in the center of the muscle to be measured without exceeding the muscle range. In some embodiments, when the electrode is in a muscle-dense area, the electrode can be located in the center of the target muscle range and away from other muscles other than the target muscle. Just as an exemplary explanation, when collecting electromyographic signals of muscles in different parts of the human body, electrodes of different lengths can be selected according to the length of the muscle fiber length direction. For example, for upper body muscles, an electrode with a length of 4 cm can be used to collect electromyographic signals. For another example, for parts with a larger range of muscles, such as the latissimus dorsi, an electrode with a length of 10 cm can be used for collection. For another example, the electrode module has a reference electrode (for example, Figure 2 When the reference electrode is smaller than the electrode for collecting electromyographic signals (for example, the third electrode 204 in FIG. 1 ), the reference electrode may be smaller than the electrode for collecting electromyographic signals (for example, Figure 2 For example, the latissimus dorsi muscle can be collected using an electrode with a length of 10 cm, and the length of the reference electrode can be 6 cm. For another example, for a muscle with a smaller range, the electrode can be a relatively small electrode, such as 2 cm or 3 cm. It can be understood that the length of the electrode refers to the length of the electrode along the direction perpendicular to the length of the muscle fiber ( Figure 1 The length of the y direction).

[0081] In some embodiments, for an electrode module including at least two electrodes, the interval between two adjacent electrodes may affect the strength of the measured electromyographic signal. Figure 1 Taking the electrode module including two electrodes (e.g., the first electrode 101 and the second electrode 102) as an example, the strength of the electromyographic signal can be reflected by the potential difference between the two electrodes. The two electrodes are along the direction of the muscle fibers ( Figure 1The electrodes are arranged at intervals along the x direction in the electrode module. When the user is exercising, the muscle to be tested will expand and contract, and there will be a potential difference along the direction of the muscle fibers. The two electrodes are arranged at intervals along the length direction of the muscle fibers to collect the potential difference of the muscle to be tested when the human body is exercising. When the spacing between the two electrodes is too small, it will affect the strength of the electromyographic signal, and if the spacing is too large, it will easily exceed the muscle range. In some embodiments, in order to improve the accuracy of the electromyographic signal, the spacing between the two electrodes (the first electrode 101 and the second electrode 102) in the electrode module can be 1mm to 10cm. Preferably, the spacing between the two electrodes in the electrode module can be 0.5cm to 6cm. Further preferably, the spacing between the two electrodes in the electrode module can be 0.8cm to 4cm. More preferably, the spacing between the two electrodes in the electrode module can be 1cm-3cm. For different muscle areas, the spacing between the two electrodes corresponding to each muscle area can be the same as or different from the spacing between the two electrodes corresponding to other muscle areas.

[0082] Combination Figure 1 , the electrode spacing in the electrode module and the electrode width in the muscle fiber direction (i.e., the x-direction) (i.e., the electrode width) are limited by the EMG frequency acquisition range and the EMG conduction velocity. Specifically, in actual measurements, different muscle movements of different individuals correspond to different EMG frequency domain performances, and different EMG frequency domains correspond to different EMG frequency acquisition ranges. In some embodiments, the EMG frequency domain acquisition range is between 10 Hz and 200 Hz. When the spacing between electrodes does not correspond to the EMG acquisition frequency range and the EMG conduction velocity, the transmission of EMG signals on the body surface will cause signal frequency domain distortion. For example, when the spacing between two electrodes receiving EMG signals is 1 cm, it can be assumed that one of the two electrodes has point a and the other electrode has point b, the distance between point a and point b is 1 cm, and the EMG signal transmission speed is 4 m / s. Then the 400 Hz signal transmitted from point a will propagate to point b and be in phase with the 400 Hz signal at point a. Then this 400 Hz signal will appear in phase at the two input ends of the differential circuit, and the strength will be suppressed by the common mode suppression effect in the circuit, resulting in a decrease in the strength of the frequency signal and distortion of the time domain signal.

[0083] Combined with the actual EMG frequency acquisition range, in some embodiments, the center spacing between the two electrodes can be less than 3 cm, so that the EMG signals within the EMG acquisition frequency range (for example, within 133 Hz) can be fully retained. In some embodiments, a larger center spacing can be used. For example, when the center spacing between the two electrodes is 6 cm, more EMG signals within the EMG acquisition frequency range (for example, within 66.5 Hz) can be retained. In the embodiments of the present specification, the center spacing between the two electrodes is the distance between the centers of the two electrodes, which can be expressed as half the width of one electrode, half the width of the other electrode, and the sum of the spacing between the adjacent edges of the two electrodes in the x direction. In some embodiments, the electrode width range can be 1 mm to 5 cm. Preferably, the electrode width range can be 0.5 cm to 3 cm. More preferably, the electrode width is 1 cm, 1.5 cm or 2 cm.

[0084] When the electrode is of a larger size, the electrode has a larger contact area with the skin, which can effectively reduce the contact impedance between the electrode and the skin. And the electrode has a larger size, so that the electrode will not fall off the skin completely in various movements or wrinkles, so as to collect electromyographic signals, and the collected electromyographic signals can be used to extract effective electromyographic signals through back-end circuits and algorithms. In addition, when the same wrinkles occur on electrodes with larger sizes and electrodes with smaller sizes, the wrinkles will have relatively less impact on the larger electrodes.

[0085] In some embodiments, the contact impedance between the electrode and the skin and the total impedance of the electrode can also be effectively reduced by using electrodes of suitable materials and structures. In some embodiments, the electrode can be an electrode composed of a single material, such as a metal fabric electrode, a conductive silicon electrode, a hydrogel electrode, a metal electrode, etc. In some embodiments, when the electrode is used to be integrated on clothing and fit the skin, preferably, the electrode can be a metal fabric electrode and a conductive silicon electrode. Further preferably, the electrode can be a metal fabric electrode, which has a smaller resistivity, and its impedance and the contact impedance with the skin are also smaller. Among them, the smaller the thickness of the metal fabric electrode, the smaller its impedance and the contact impedance with the skin. In some embodiments, when using a metal fabric electrode to collect electromyographic signals, the thickness of the metal fabric electrode can be 10μm to 5mm. Preferably, the thickness of the metal fabric electrode can be 100μm to 3mm. Further preferably, the thickness of the metal fabric electrode can be 500μm to 2mm. In some embodiments, the electrode can also be an electrode formed by superimposing different materials, such as a metal fabric conductive silicon composite material electrode composed of a metal fabric material and a conductive silicon material. Not only does it have a small contact impedance with the skin, but the conductive silicon in contact with the skin has the advantages of being skin-friendly and washable, thus avoiding discomfort to the human body caused by contact between the electrode and the skin.

[0086] In practical applications, one end of the electrode is connected to the skin and can be regarded as a surface, while the other end is connected to the wire and can only be regarded as a point. However, in certain cases (for example, when the electrode material has good conductivity), it can still be regarded as a surface. Therefore, the contact between the electrode and the skin can generally be equivalent to the following: Figure 4 The electrode impedance parallel model shown in the figure is equivalent to when the electrode material has good conductivity. Figure 4 In this example, R1=0, R2=0.

[0087] exist Figure 4 In the equation, R1 represents the longitudinal impedance of the electrode material, R2 represents the transverse impedance of the electrode material, R3 represents the transverse impedance of the skin surface, R4 represents the longitudinal impedance of the skin (for the convenience of explanation and description, the longitudinal impedance of the skin here includes the contact impedance), R5 is the transverse impedance of the dermis, EMG represents the electromyographic signal source, and the measurement point is the lead-out point of the conductive wire on the electrode. Among them, R1 and R2 are related to the material (resistivity), structure and size of the electrode (thickness is perpendicular to the skin surface direction, and length is parallel to the skin surface direction). Since the resistivity of human skin is a physiological characteristic, R3 and R4 can be fixed values, but R5 will also be affected by the length of the electrode. Therefore, the electrode impedance parallel model can be optimized by changing the material, structure and size of the electrode (for example, by changing the size of R1 and R2 to change the parallel path in the electrode impedance parallel model, so as to achieve the purpose of reducing the total impedance and contact impedance of the electrode), so that suitable materials can be selected for the electrode and suitable structures can be designed.

[0088] In some embodiments, since the skin surface is the stratum corneum of human skin, the stratum corneum is relatively dry and has a large resistivity, R3 has a large value and can be considered as an open circuit. In addition, due to symmetry, the signal sources are basically the same, so only one EMG signal source can be considered.

[0089] In some embodiments, electrodes made of different materials correspond to different electrode parallel impedance models, and the parallel path in the corresponding electrode impedance parallel model can be changed by changing the structure of the electrode, thereby achieving the purpose of reducing the total electrode impedance and the contact impedance between the electrode and the skin.

[0090] For example, Figure 5 This is a conductive silicon electrode impedance parallel model shown in some embodiments of the present application. Since the resistivity of conductive silicon is large, R1 and R2 cannot be ignored, and R1 and R2 of electrodes with different structures and sizes will also vary greatly. Resistivity will have the same effect on R1 and R2, while thickness will have different effects on R1 and R2. Among them, R2 is affected by thickness. The greater the thickness, the smaller R2. Therefore, R2 can be regarded as a parallel connection of a series of lateral resistances r2 of materials with unit thickness. Figure 5As shown, R1 is also affected by the thickness. The larger the thickness, the larger R1 is. Therefore, R1 can be regarded as a series of longitudinal resistances r1 of a series of materials with unit thickness.

[0091] Through Figure 5 The electrode impedance model of the conductive silicon electrode shown can be derived Figure 6 The relationship between the resistance of the conductive silicon electrode and its thickness. Figure 6 It can be seen that the greater the thickness of the conductive silicon electrode, the smaller its resistance. For electrodes of materials with higher resistivity (such as conductive silicon electrodes), the thickness of the electrode can be increased to reduce the electrode transverse resistance R2, so that a larger area of ​​the path can participate in the parallel model (for example, assuming that the resistance of the parallel path is more than 10 times that of the minimum resistance path, the smaller electrode transverse resistance R2 can bring a larger area of ​​the path to participate in the parallel connection), and the parallel connection can greatly reduce the total impedance and contact impedance. In some embodiments, the thickness of the conductive silicon electrode can be 0.01mm-4mm. Preferably, the thickness of the conductive silicon electrode can be 0.1mm-3mm. Further preferably, the thickness of the conductive silicon electrode can be 0.5mm-1mm. In some embodiments, the width of the conductive silicon electrode is 1mm to 5cm. Preferably, the length of the conductive silicon electrode is 0.5cm to 3cm. Further preferably, the width of the conductive silicon electrode is 1cm, 1.5cm or 2cm. In some embodiments, the length of the surface of the conductive silicon electrode used to contact the skin can be 1cm to 10cm. It should be noted that the length of the conductive silicon electrode can be determined according to the measurement part. For example, for upper body muscles, a conductive silicon electrode with a length of 4 cm can be used to collect electromyographic signals. For another example, for a part with a larger range of muscles, such as the latissimus dorsi, a conductive silicon electrode with a length of 10 cm can be used for collection.

[0092] In some embodiments, electrodes of different materials may be combined to reduce the total impedance of the electrodes. For exemplary purposes only, a metal fabric conductive silicon composite material electrode is used as an example for description. Fig. 7A It is a schematic diagram of the structure of electrodes according to some embodiments of the present application. Figure 7B According to some embodiments of the present application Figure 4 The parallel model when R5 is much larger than R2. Fig. 7A As shown, the metal fabric conductive silicon composite material electrode may include a base structure 701, a metal fabric electrode 720 and a conductive silicon electrode 710 arranged in sequence from top to bottom. The lower surface of the conductive silicon electrode 710 contacts the skin, and the metal fabric electrode 720 is between the upper surface of the conductive silicon electrode and the base structure 701 made of a material with a lower conductivity. Furthermore, the metal fabric electrode has a high conductivity and can be approximately regarded as a material lateral resistance that short-circuits the conductive silicon electrode 710 (for example, Figure 4 and Figure 7B This helps to reduce the resistance of the electrode parallel circuit ( Figure 4 The parallel circuit in is twice R2 plus one R1, Figure 7B The parallel circuit in is an R2 plus R1), which can realize parallel connection of more channels and larger areas, thereby greatly reducing the total impedance and contact impedance, and making the measurement results of the electrode along the muscle fiber direction (i.e., the collected electromyographic signals) consistent. The metal fabric conductive silicon composite material electrode formed by combining the metal fabric electrode 720 and the conductive silicon electrode 710 greatly reduces the total impedance of the electrode compared with the simple conductive silicon electrode. In addition, due to the realization of parallel connection of more channels and larger areas, the contact impedance between the electrode and the skin can also be effectively reduced, so that in the case of year-on-year fluctuations, the value of the contact impedance fluctuation relative to the circuit input impedance can be reduced, thereby reducing the noise in the electromyographic signal. And when the metal fabric conductive silicon composite material electrode is used to collect electromyographic signals, the conductive silicon electrode is in direct contact with the human skin. The conductive silicon has the advantages of skin-friendly and strong tolerance, which can avoid the discomfort caused to the human body by the contact between the electromyographic signal collection electrode and the skin. In some embodiments, the thickness of the metal fabric electrode in the metal fabric conductive silicon composite material electrode can be 10μm to 5mm. Preferably, the thickness of the metal fabric electrode in the metal fabric conductive silicon composite material electrode can be 100μm to 3mm. Further preferably, the thickness of the metal fabric electrode in the metal fabric conductive silicon composite electrode may be 500 μm to 2 mm. In some embodiments, the thickness of the conductive silicon electrode in the metal fabric conductive silicon composite electrode may be 1 μm to 4 mm. Preferably, the thickness of the conductive silicon electrode in the metal fabric conductive silicon composite electrode may be 10 μm to 2 mm. Further preferably, the thickness of the conductive silicon electrode in the metal fabric conductive silicon composite electrode may be 0.1 mm to 1 mm. In some embodiments, the width of the metal fabric conductive silicon composite electrode is 1 mm to 5 cm. Preferably, the width of the metal fabric conductive silicon composite electrode is 0.5 cm to 3 cm. Further preferably, the width of the metal fabric conductive silicon composite electrode is 1 cm, 1.5 cm or 2 cm. In some embodiments, the length of the surface of the metal fabric conductive silicon composite electrode for contact with the skin may be 1 cm to 10 cm. It should be noted that the length of the combined electrode can be determined according to the measurement part. For example, for upper body muscles, a combined electrode with a length of 4 cm can be used to collect electromyographic signals. For another example, for a part with a larger range of muscles, such as the latissimus dorsi, a combined electrode with a length of 10 cm can be used for collection.

[0093] In some embodiments, the size (e.g., length and width) of the metal fabric electrode is larger than that of the conductive silicon electrode. For example, the width of the metal fabric electrode is 1 mm to 5 cm, and the width of the conductive silicon electrode is 0.8 cm to 4 cm. Preferably, the width of the metal fabric electrode is 0.5 cm to 3 cm, and the width of the conductive silicon electrode is 0.4 cm to 2.8 cm. Further preferably, the width of the metal fabric electrode is 1 cm to 2 cm, and the width of the conductive silicon electrode is 0.8 cm to 1.6 cm. In some embodiments, the length of the metal fabric electrode in the electrode combined with the conductive silicon electrode and the metal fabric electrode can be 1 cm to 10 cm. The length of the conductive silicon electrode in the electrode combined with the conductive silicon electrode and the metal fabric electrode can be 0.8 cm to 8 cm. It should be noted that the length of the conductive silicon electrode and the metal fabric electrode can be determined according to the measurement part. For example, for the upper body muscles, a combined electrode with a length of 4 cm can be used to collect electromyographic signals. The length of the metal fabric electrode can be 4 cm, and the length of the conductive silicon electrode can be 3.2 cm. For another example, for a muscle area with a larger range, such as the latissimus dorsi muscle, a combined electrode with a length of 10 cm can be used for collection. The length of the metal fabric electrode can be 10 cm, and the length of the conductive silicon electrode can be 8 cm.

[0094] Limb movement may cause the electrode to shift or wrinkle relative to the skin or even fall off the skin, resulting in large contact impedance fluctuations and even failure to collect electromyographic signals. In addition, electrode displacement may also change the position of collecting electromyographic signals, resulting in inaccurate collected electromyographic signals. In some embodiments, the possibility of the electrode moving relative to the skin can be reduced by increasing the tightness of the fit between the electrode and the skin. Furthermore, the close fit between the electrode and the skin can also shorten the distance between the electrode and the skin. According to formula (1), the contact impedance between the skin and the electrode can be reduced, which is conducive to reducing the contact impedance and reducing the fluctuation of the contact impedance.

[0095] In some embodiments, in order to achieve a tight and reliable fit between the electrode and the skin, the electrode module may include a plurality of protruding structures, which may be located between the electrode and the base structure, and the protruding structure may make the surface of the electrode protrude outward. In some embodiments, the protruding structure may be arranged in an array on the surface of the electrode or / and the surface of the base structure, or may be randomly distributed. Specifically, when a certain external pressure acts on the electrode module to make the electrode contact the human skin, the protruding structure may make the electrode have a better fit with the human skin. On the other hand, by setting a protruding structure, the pressure requirement of the carrier (e.g., clothing) where the electrode module is located on the body can be reduced. The electrode module with a protruding structure ensures that only the electrode part has a large pressure, and the pressure of the carrier on other parts of the body is not large, which ensures that the electrode has a good fit while making the user feel comfortable. In some embodiments, the electrode may be a protruding structure. For example, the middle area of ​​the electrode is higher than the edge area of ​​the electrode. In some embodiments, the electrode may be a planar structure, and the electrode may protrude outward relative to the base structure of the electrode module to form a protruding structure of the electrode module. In some embodiments, the height of the protruding structure is 1 mm to 10 mm. Preferably, the height of the protruding structure is 2 mm to 8 mm. More preferably, the height of the raised structure is 2mm to 4mm. It should be noted that the raised structure here is a raised structure with the highest in the middle and gradually lower on the four sides, and the height of the raised structure is the height of the part at the highest position in the middle of the raised structure. In some embodiments, the raised structure can also be a structure in which the end face in contact with the human body is approximately a plane, and the height of the raised structure can be 0.5mm to 5mm. Preferably, the height of the raised structure can be 1mm to 4mm. More preferably, the height of the raised structure can be 1mm to 2mm. In some embodiments, the raised structure can also be located on the other side of the base structure, that is, the raised structure and the electrode are distributed on different surfaces of the base structure. In some embodiments, the raised structure can be made of an elastic material, for example, the raised structure can be made of soft PVC, resin, silicone and other materials. In some embodiments, the raised structure can be a hollow structure, and the raised structure can include a filler, which can be located in the hollow interior of the raised structure. The filler can be an elastic material with a certain conductivity. For example, the filler can contain a water-absorbing sponge, silicone, etc. On the one hand, the filler can remove excess moisture from the skin surface and prevent short circuits between electrodes.

[0096] Considering that the pressures on the protruding structures at the two electrodes are different, the deformations of the protruding structures at the two electrodes are different, so that the contact impedances between the two electrodes and the skin are different, thereby affecting the consistency between the two electrodes differently, so that the collected electromyographic signals are affected by noise. In some embodiments, the noise in the electromyographic signal can be reduced by reducing the contact impedance. In some embodiments, the contact impedance fluctuation range can also be controlled to reduce the noise in the electromyographic signal. In some embodiments, the contact impedance fluctuation can be within 1M ohm. Preferably, the contact impedance fluctuation can be within 100K ohm. More preferably, the contact impedance fluctuation can be within 10K ohm. Controlling the contact impedance fluctuation range can be that the contact impedance range between the two electrodes and the skin is within a specific range (for example, within the above-mentioned 1M ohm, within 100K ohm, and within 10K ohm), or the fluctuation values ​​of the contact impedance between the two electrodes and the skin are approximately the same. In some embodiments, noise can also be reduced by the circuit connected to the electrode, for example, the circuit connected to the electrode can include a differential architecture, a notch filter, a threshold filter, a right leg drive, etc. In some embodiments, the problem of inconsistent contact impedance between the two electrodes and the skin can also be solved by adjusting the structure and height of the protruding structure. For example, the protruding structure is a solid structure, and the end surface of the protruding structure in contact with the skin is a plane. For another example, the height of the protruding structure is 1 mm.

[0097] In some embodiments, the electrode module may include multiple suction cup structures, which can make the electrodes fit more closely to the skin, prevent the electrodes from moving when collecting electromyographic signals, and ensure the accuracy of the collected electromyographic signals. Figure 8 is a cross-sectional view of a suction cup structure according to some embodiments of the present application. Figure 8As shown, the suction cup structure 800 is a regular or irregular geometric structure, such as a three-dimensional structure such as a cylinder, a truncated cone, a cuboid, etc., wherein the suction cup structure 800 may include a hollow portion 810, and the hollow portion has an opening 811 at the end of one end of the suction cup structure 800. In some embodiments, at least part of the suction cup structure 800 may be made of an elastic material such as a thermoplastic elastomer (TPE), polypropylene (PPE), and a polyurethane-acrylate polymer (s-PUA), so that the suction cup structure 800 can have the ability to deform. When the electrode module is attached to the skin, the opening 811 of the hollow portion 810 in the suction cup structure 800 contacts the human skin. Under the action of an external force, the suction cup structure 800 is deformed, so that part of the air inside the hollow portion 810 is squeezed to the outside, so that the external air pressure is greater than the internal air pressure of the hollow portion 810, and a negative pressure space is formed with the skin surface, so that the electrode module (or electrode) is adsorbed on the skin, and the electrode and the skin are closely attached. In some embodiments, the shape of the hollow portion 810 includes but is not limited to a sphere, an arch, a column, a cube, a broken sphere, and other regular or irregular shapes. Figure 8 The hollow part of the suction cup structure shown is in the shape of a cube. Fig. 9 The shape of the hollow portion of the suction cup structure shown is an incomplete sphere.

[0098] Fig.10 It is a cross-sectional view of another suction cup structure shown in some embodiments of the present application. In some embodiments, the suction cup structure 1000 may include an intermediate structure 1020, and the intermediate structure 1020 is located at the hollow part 1010 of the suction cup structure 1000, wherein a part of the intermediate structure 1020 may be connected to the side wall of the suction cup structure 1000 where the hollow part 1010 is located. In some embodiments, the intermediate structure 1020 may be made of a material that is soft and easy to deform, and has a certain elasticity. For example, the intermediate structure 1020 may be made of soft PVC, silica gel, sponge and other materials. In some embodiments, the shape of the intermediate structure 1020 may include but is not limited to spherical, cylindrical, cubic and other regular or irregular shapes. In some embodiments, the intermediate structure 1020 may be a part of the suction cup structure 1000, or it may be set separately from the suction cup structure 1000. In some embodiments, the intermediate structure 1020 may separate the hollow part 1010 into a plurality of interconnected spatial regions, thereby improving the applicability of the electrode module in a specific environment (for example, an environment with more liquid on the skin surface). As an exemplary illustration only, as Fig.10 As shown, the intermediate structure 1020 is connected to the suction cup structure 1000, and the connection is represented by point a. When the intermediate structure is located in the hollow part 1010 of the suction cup structure 1000, other parts of the intermediate structure 1020 (for example, Fig.10Point b and point c) shown in the figure are in contact with the side wall of the suction cup structure 1000 where the hollow part 1010 is located instead of being connected. The contact here is through the elasticity of the elastic intermediate structure 1020 and the squeezing force between the side wall of the suction cup structure 1000. The intermediate structure 1000 can separate the hollow part into space area 1, space area 2 and space area 3. Specifically, space area 1 and space area 3 are formed by the intermediate structure 1020 and the side wall of the suction cup structure 1000, and space area 3 is formed by the intermediate structure 1020, the side wall of the suction cup structure 1000 and the human skin, wherein space area 1, space area 2 and space area 3 are interconnected. Specifically, when the suction cup structure 1000 is applied to an environment with a large amount of liquid on the skin surface (for example, parts of the human body that are prone to sweating (armpits, chest, etc.)), in the absence of external forces, the liquid (sweat) exists in the spatial region 3. When an external force (for example, the force generated by muscle movement) acts on the suction cup structure 1000, for example, when the suction cup structure 1000 is squeezed, the suction cup structure 1000 and the intermediate structure 1020 will be deformed, and the liquid in the spatial region 3 will reach the spatial region 1 and the spatial region 2 through points b and c. After the squeezing is completed, the suction cup structure 1000 and the intermediate structure 1020 restore their shapes, and part of the liquid in the spatial region 3 will remain in the spatial region 1 and the spatial region 2, and the amount of liquid in the spatial region 3 will be greatly reduced relative to the amount of liquid when not squeezed, thereby generating a strong negative pressure adsorption force between the suction cup structure 1000 and the human skin.

[0099] Fig.11 is a cross-sectional view of a suction cup structure provided according to some embodiments of the present application. Fig.11As shown, the body of the suction cup structure 1100 has a middle part 1110, the middle part 1110 has an opening 1111 facing the skin, and has an intermediate structure 1120 inside the middle part 1110. Due to the existence of the intermediate structure 1120, the cavity may include an upper space 1112 and a lower space 1113. In some embodiments, the suction cup structure 1100 may be made of an elastic material (e.g., polyurethane-acrylate polymer (s-PUA)), and the suction cup structure 1100 and its intermediate structure 1120 may be deformed under the action of an external force. When collecting electromyographic signals, the electrode with the suction cup structure 1100 may be placed at the part of the human body where the electromyographic signal is to be collected, and then a pressure is applied to the suction cup structure 1100 so that the suction cup structure 1100 contacts the human skin, and the suction cup structure 1100 works at this time. When the suction cup structure 1100 is working, the upper space 1112 of the middle part 1110 of the suction cup structure 1100 will change, and the lower space 1113 will also change accordingly. For example, the middle structure 1120 inside the suction cup structure 1100 expands outward, and the outer side wall shrinks inward at the same time, and part of the air in the upper space 1112 and the lower space 1113 is discharged to the outside, and the external air pressure is greater than the internal air pressure of the suction cup structure 1100, thereby forming a negative pressure space, and the electrode can be tightly and reliably adsorbed on the skin under the action of the negative pressure adsorption force of the suction cup structure 1100. In some embodiments, a certain amount of PBS buffer can be loaded in the middle part 1110 of the suction cup structure 1100 to improve its adsorption capacity.

[0100] In some embodiments, Fig.12 is a schematic diagram of the structure of an electrode module with a suction cup structure according to some embodiments of the present application. Fig.12As shown, a suction cup structure 1210 (e.g., suction cup structure 800, suction cup structure 1100) can be provided on the electrode module 1200, and the array is distributed around the electrode (e.g., electrode 1201 and electrode 1202). A plurality of suction cup structures 1210 are distributed around the electrode in an array, and are located on the side of the base structure 1203 of the electrode module 1200 facing the skin together with the electrode, and the suction cup structure 1210 has the same or similar height or thickness as the electrode, so that the electrode module can be tightly and reliably adsorbed on the skin through the suction cup structure, and the electrode can be in full contact with the skin, so that the electromyographic signal can be accurately collected. It should be noted that a plurality of suction cup structures 1210 can also be randomly distributed around the electrode. In addition, when the suction cup structure 1210 is far away from the electrode, the height of the suction cup 1210 can be greater than or less than the height of the electrode. When the suction cup is made of a soft and easily deformable material, the suction cup structure 1210 can also be higher than the electrode while being close to the electrode. It is only necessary to ensure that after the user wears an item with an electrode module (for example, clothes), the pressure of the item ensures that the suction cup 1210 is deformed without affecting the electrode's contact with the skin.

[0101] In some embodiments, the suction cup structures may be arranged in an array on the electrode, or may be randomly distributed. Fig.13 FIG. 1 is a schematic diagram of another electrode module with a suction cup structure according to some embodiments of the present application. Fig.13 As shown, multiple suction cup structures 1310 are evenly distributed on the side of the electrode (for example, electrode 1301 and electrode 1302) for contacting the skin. Since the electrode and the skin are indirectly connected through the suction cup structure, in order to ensure that the electrode can collect the electromyographic signal, the material of the suction cup structure 1310 can be partially or completely selected from conductive materials. In some embodiments, the conductive material may include conductive silicone, conductive resin, conductive plastic, etc. In this embodiment, by arranging multiple suction cup structures 1310 in an array on or between the base structure 1303 of the electrode module 1300, the multiple suction cup structures are evenly arranged on the electrode, so that the electrode can be more evenly and firmly attached to the skin. In some embodiments, multiple suction cup structures 1310 can also be randomly arranged on the base structure 1303 of the electrode module 1300 or on the electrode.

[0102] It should be noted that the suction cup structure 1210 and the suction cup structure 1310 may include Figure 8-11 The suction cup structure shown is not described in detail here. In other embodiments, the electrode can also be closely and reliably attached to the skin by means of gluing, clamping, etc.

[0103] In some embodiments, in order to further prevent the electrode from being relatively displaced on the skin, the electrode module may further include a plurality of convex structures (not shown in the figure), which may increase the friction between the electrode module or the electrode and the skin, thereby increasing the anti-slip performance of the electrode module. The convex structure may be located on the base structure or the electrode and may refer to the surface in contact with the human skin. Among them, the convex structure may be of any shape and may be arrayed or randomly distributed on the base structure of the electrode or the electrode module. In some embodiments, the shape of the convex structure may include regular or irregular structures such as conical, cylindrical, cuboid, hemispherical, etc. In some embodiments, in order to improve the anti-slip performance of the electrode module, the height of the convex structure may be 5μm to 200μm. Preferably, the height of the convex structure may be 10μm to 100μm. Further preferably, the height of the convex structure may be 20μm to 80μm. More preferably, the height of the convex structure may be 20μm to 50μm. In some embodiments, in order to improve the anti-slip performance of the electrode module, the size of the connection surface between the convex structure and the electrode or substrate structure (for example, length, width or radius, etc.) can be 10μm to 1000μm. Preferably, the size of the connection surface between the convex structure and the electrode or substrate structure can be 50μm to 800μm. Further preferably, the size of the connection surface between the convex structure and the electrode or substrate structure can be 100μm to 600μm. In some embodiments, in order to improve the anti-slip performance of the electrode module, the distribution density of the convex structure can be 1 / 2.25mm 2 ~10pcs / 2.25mm 2 Preferably, the distribution density of the bump structure can be 3 / 2.25mm 2 ~8pcs / 2.25mm 2 Further preferably, the distribution density of the bump structure can be 5 / 2.25mm 2 ~6pcs / 2.25mm 2 As an example only, the bump structure can be randomly distributed on the conductive silicon electrode, and its shape is conical, the height is 20-50 μm, the radius of the cone bottom is 100-600 μm, and the distribution density of the bump structure is 5 / 2.25 mm 2 The conductive silicon electrode has good anti-slip performance. In some embodiments, the bump structure can also be arranged between the electrodes to block the sweat and other body surface liquids between the electrodes to prevent the electrodes from short-circuiting.

[0104] Since the collection of electromyographic signals usually needs to be completed when people are exercising, during the exercise, as the heat is consumed, the sweat discharged by the human body accumulates between the electrode and the skin. Due to the viscosity of sweat and human skin and the viscosity of sweat and electrodes, the electrode and skin will fit too closely, causing the skin to be unable to breathe, and it is also easy to breed bacteria. In addition, the accumulation of sweat will also cause the problem of short circuit between electrodes. In order to prevent the occurrence of the above problems, the electrode module can also include a number of air holes, which can be located on the base structure or electrode of the electrode module so that the electrode module has a certain air permeability, promote the air permeability of the skin and the external environment, and reduce the accumulation of sweat between the electrode module and the human skin. In some embodiments, the shape of the air hole can be regular or irregular shapes such as circular, oval, rectangular, square, hexagonal, etc. In some embodiments, a number of air holes can be arranged in an array. In some embodiments, the diameter range of the air hole can be 0.2mm-4mm. Preferably, the diameter range of the air hole is 0.5mm~3mm. Further preferably, the diameter range of the air hole is 1mm~2mm. More preferably, the diameter of the air holes is 1 mm, 1.5 mm or 2 mm. In some embodiments, the total area of ​​the air holes does not exceed 90% of the electrode area. Preferably, the total area of ​​the air holes does not exceed 50% of the electrode area. Further preferably, the total area of ​​the air holes does not exceed 20% of the electrode area. In some embodiments, the air holes can be made by mechanical punching.

[0105] The electrode module provided in the embodiment of the present application can not only be integrated into clothing or other wearable devices to effectively collect the electromyographic signals of various parts of the user's body during exercise. It can also be used in medical rehabilitation engineering to collect the electromyographic signals of patients, so as to make corresponding diagnosis or treatment for the patients. Or in bionics, it can be used to collect electromyographic signals to study artificial prostheses.

[0106] Fig.14 is an exemplary structural diagram of a wearable device according to some embodiments of the present application. Fig.14 As shown, the wearable device 1400 may include a top garment 1410 and a trouser garment 1420. The top garment 1410 may include a top garment base 14110, at least one top garment data processing module 14120, at least one top garment sensor module 14130, etc., wherein at least one top garment data processing module 14120 and at least one top garment sensor module 14130 are located in areas of the top garment base 14110 that fit different parts of the human body. The top garment base 14110 may refer to clothing worn on the upper body of a human body. In some embodiments, the top garment base 14110 may include a short-sleeved T-shirt, a long-sleeved T-shirt, a shirt, a jacket, etc. Referring to Fig.14, at least one top data processing module 14120 may include a first top data processing module 14121 and a second top data processing module 14122. Specifically, the first top data processing module 14121 may be arranged at the left shoulder position of the top garment base 14110, and the second top data processing module 14122 may be arranged at the right shoulder position of the top garment base 14110. It should be noted that the first top data processing module 14121 and the second top data processing module 14122 may be symmetrically distributed with respect to the midline of the top garment base 14110, or may be asymmetrically distributed with respect to the midline of the top garment base 14110. At least one top sensor module 14130 may include a first top sensor module 14131 and a second top sensor module 14132. Among them, the first top sensor module 14131 may include one or more sensors of the same or different types, for example, an electromyographic sensor (also referred to as an electromyographic module), an electrocardiographic sensor, a respiratory sensor, a temperature sensor, a humidity sensor, etc. The first tops sensor module 14131 can be arranged at the left muscle position (e.g., left arm biceps brachii, left arm wrist extensor, left pectoralis major, etc.) of the tops clothing base 14110. The second tops sensor module 14132 can refer to one or more sensors of the same or different types, e.g., electromyographic sensor, electrocardiographic sensor, respiratory sensor, temperature sensor, humidity sensor, etc. The second tops sensor module 14132 can be arranged at the right muscle position (e.g., right arm biceps brachii, right arm wrist extensor, right pectoralis major, etc.) of the tops clothing base 14110. In certain embodiments, the first tops data processing module 14121 can be connected to the first tops sensor module 14131 by electrode routing, and the second tops data processing module 14122 can be connected to the second tops sensor module 14132 by electrode routing. In some embodiments, the first top data processing module 14121 and the first top sensor module 14131 can be connected to each other by wireless communication, and the second top data processing module 14122 and the second top sensor module 14132 can be connected to each other by wireless communication. For example, the myoelectric sensor of the first top sensor module 14131 can transmit the collected human body electromyographic signals to the first top data processing module 14121 by wire or wirelessly. It should be noted that the specific content of the myoelectric sensor (electrode module) here can be referred to elsewhere in this application (for example, Figure 1-Figure 3 Figure 7- Fig.13 ) is described here and will not be elaborated on.

[0107] In some embodiments, the left shoulder position of the upper garment base 14110 is provided with a first upper garment data processing module 14121, and the first upper garment data processing module 14121 is configured to receive upper body motion data of a sensor on the left side of the human body (e.g., an electromyographic sensor, an electrocardiographic sensor, a respiratory sensor, etc.). The right shoulder position of the upper garment base 14110 is provided with a second upper garment data processing module 14122, and the second upper garment data processing module 14122 is configured to receive upper body motion data of a sensor on the right side of the human body (e.g., an electromyographic sensor, an electrocardiographic sensor, a respiratory sensor, etc.). The first upper garment data processing module 14121 at the left shoulder position and the second upper garment data processing module 14122 at the right shoulder position mentioned above can be symmetrically distributed with respect to the midline of the upper garment base 14110.

[0108] In some embodiments, the first top data processing module 14121 at the left shoulder position and the second top data processing module 14122 at the right shoulder position may be in a master-slave relationship. For example, the first top data processing module 14121 is a master data processing module, and the second top data processing module 14122 is a slave data processing module. At this time, the first top data processing module 14121 and the second top data processing module 14122 may be connected to each other by wired or wireless communication. Specifically, the first top data processing module 14121 receives motion data on the left side of the human body, and the second top data processing module 14122 receives motion data on the right side of the human body. The second top data processing module 14122 may pass the received motion data on the right side of the human body to the first top data processing module 14121 for processing. In some embodiments, the routing mode between the first top data processing module 14121 and the second top data processing module 14122 may be the front side routing of the wearable device 1400, or the back side routing of the wearable device 1400. In some embodiments, the first top data processing module 14121 can also transmit the left side human body motion data received by itself and the right side human body motion data received from the second top data processing module 14122 to the external terminal, and the external terminal processes the received motion data.

[0109] In some embodiments, the first top data processing module 14121 and the second top data processing module 14122 can also be in a parallel relationship. When the first top data processing module 14121 and the second top data processing module 14122 are in a parallel relationship, the first top data processing module 14121 and the second top data processing module 14122 can be connected to the external terminal for communication respectively. Specifically, the first top data processing module 14121 receives the motion data from the left side of the human body, and passes the received motion data on the left side of the human body to the external terminal, and the external terminal performs data processing on the received motion data on the left side of the human body. The second top data processing module 14122 receives the motion data from the right side of the human body, and passes the received motion data on the right side of the human body to the external terminal, and the external terminal performs data processing on the received motion data on the right side of the human body.

[0110] In some embodiments, the human motion data received by the upper garment data processing module 14120 can be processed in the upper garment data processing module 14120. For example, the human body left motion data received by the first upper garment data processing module 14121 is processed in the first upper garment data processing module 14121, and the first upper garment data processing module 14121 transmits the processed motion data to the peripheral terminal. In some embodiments, the human body motion data received by the upper garment data processing module 14120 can also be processed in the peripheral terminal. For example, the second upper garment data processing module 14122 directly transmits the received human body right motion data to the peripheral terminal, and the peripheral terminal processes the received human body right motion data. In some embodiments, the human body motion data received by the upper garment data processing module 14120 can also be processed in part in the upper garment data processing module 14120, and another part in the peripheral terminal. For example, the first top data processing module 14121 performs a part of data processing on the left side movement data of the human body received by the first top data processing module 14121, and the first top data processing module 14121 transmits the motion data after the part of data processing to the external terminal, and the external terminal then performs another part of data processing on the received motion data after the part of data processing.

[0111] In some embodiments, the upper garment data processing module 14120 and the peripheral terminal can communicate bidirectionally. For example, the first upper garment data processing module 14121 (or the second upper garment data processing module 14122) can transmit motion data to the peripheral terminal, and can also receive instructions from the peripheral terminal. For example, the instruction can be an instruction to control the operation of the electrode module, or an instruction to provide motion quality feedback based on the user's motion data.

[0112] Continue to refer to Fig.14, the trousers garment 1420 may include a trousers garment base 14210, at least one trousers data processing module 14220, at least one trousers sensor module 14230, etc. Among them, at least one trousers data processing module 14220 may include a first trousers data processing module 14221 and a second trousers data processing module 14222. Specifically, the first trousers data processing module 14221 may be arranged at the left crotch position of the trousers garment base 14210, and the second trousers data processing module 14222 may be arranged at the right crotch position of the trousers garment base 14210. It should be noted that the first trousers data processing module 14221 and the second trousers data processing module 14222 may be symmetrically distributed with respect to the midline of the trousers garment base 14210, or may be asymmetrically distributed with respect to the midline of the trousers garment base 14210. At least one trousers sensor module 14230 may include a first trousers sensor module 14231 and a second trousers sensor module 14232. Among them, the first pants sensor module 14231 can include one or more different types of sensors, such as electromyographic sensors, temperature sensors, humidity sensors, etc. The first pants sensor module 14231 can be set at the left muscle position of the left leg of the pants clothing base 14210 (for example, the left gluteus maximus, the left vastus lateralis, the left vastus medialis, the left biceps femoris, etc.). In some embodiments, the first pants sensor module 14231 can be set at the front muscle position of the left leg and the rear muscle position of the left leg of the pants clothing base 14210. The second pants sensor module 14232 can include one or more different types of sensors, such as electromyographic sensors, temperature sensors, humidity sensors, etc. The second pants sensor module 14232 can be set at the right muscle position of the right leg of the pants clothing base 14210 (for example, the right gluteus maximus, the right vastus lateralis, the right vastus medialis, the right biceps femoris, etc.). In some embodiments, the second pants sensor module 14232 can be set at the front muscle position of the right leg and the rear muscle position of the right leg of the pants clothing base 14210. In some embodiments, the first trousers data processing module 14221 and the first trousers sensor module 14231 may be connected by electrode wiring, and the second trousers data processing module 14222 and the second trousers sensor module 14232 may be connected by electrode wiring. The contents of at least one trousers data processing module 14220 (e.g., the first trousers data processing module 14221 and the second trousers data processing module 14222) and at least one trousers sensor module 14230 (e.g., the first trousers sensor module 14231 and the second trousers sensor module 14232) can refer to the relevant contents of at least one top data processing module 14120 and at least one top sensor module 14130, and will not be repeated here.

[0113] In some embodiments, the sensor modules (for example, the first top sensor module 14131, the second top sensor module 14132, the first pants sensor module 14231, the second pants sensor module 14232) may include but are not limited to electromyography sensors, inertial sensors, electrocardiogram sensors, respiratory sensors, temperature sensors, humidity sensors, acid-base sensors, sound wave transducers, etc.

[0114] In some embodiments, the electromyographic sensor (also referred to as the electrode module) can be set at the human muscle position, and the electromyographic sensor can be connected to the data processing module (for example, the first top data processing module 14121, the second top data processing module 14122, the first pants data processing module 14221, and the second pants data processing module 14222) for communication. Among them, the upper body muscle position can include but is not limited to the biceps, triceps, wrist extensors, wrist flexors, deltoids (for example, the anterior head of the deltoid, the middle head of the deltoid, the posterior head of the deltoid), the trapezius, the latissimus dorsi, the pectoralis major, the external oblique abdominal muscles, the rectus abdominis, etc. The trousers muscle position can include but is not limited to the gluteus maximus, the vastus lateralis, the vastus medialis, the rectus femoris, the biceps femoris, the tibialis anterior, the gastrocnemius, etc. In some embodiments, the electromyographic sensor can be configured to collect muscle information when the user is exercising, such as movement amplitude, movement speed, movement intensity, etc. For example, when a user performs a barbell bench press, the myoelectric sensor arranged in the biceps (or triceps, deltoid, pectoralis major, etc.) can collect muscle information (such as movement amplitude, movement speed, movement intensity, etc.) of the corresponding position of the user, and transmit the collected muscle information to the data processing module. The data processing module performs data processing on the received muscle information (or the data processing module transmits the received muscle information to the peripheral terminal, and the peripheral terminal performs data processing on the received muscle information), and determines whether the muscle data of the user during the barbell bench press is within the judgment standard. If the judgment standard is exceeded, the wearable device can warn the user through the feedback module. The judgment standard here can be the muscle data of professionals (such as athletes, coaches, etc.) entered in advance in the wearable device and a large number of ordinary people in the barbell bench press process, and is adjusted and adapted according to the user's information at the same time. The user can understand in real time whether the muscle state of his own barbell bench press (such as movement amplitude, movement speed, movement intensity, etc.) is standardized according to the warning of the feedback module, and adjust the exercise posture in time.

[0115] In some embodiments, the inertial sensor can be integrated into the sensor module. In this case, the inertial sensor can be separated from the data processing module, thereby causing practical problems. For example, washing problems, complexity problems (for example, separate production, disassembly, etc.), power supply problems, charging problems, etc. In some embodiments, the inertial sensor can also be arranged in the left data processing module and the right data processing module of the clothing base, and the inertial sensor can be configured to monitor the user's motion parameters (such as the number of steps, stride, step frequency, etc.). Specifically, the inertial sensor is arranged in the left data processing module and the right data processing module of the clothing base. On the one hand, the user's motion parameters, such as the number of steps, stride, step frequency, etc., can be monitored. On the other hand, the problem of the inertial sensor being separated from the data processing module (such as washing problems, power supply problems, etc.) can be effectively solved. On the other hand, the inertial sensors respectively arranged in the first data processing module and the second data processing module can also monitor the coordination and consistency of the movements on the left and right sides of the user's body, balance, etc.

[0116] In some embodiments, more inertial sensors can be designed inside and / or outside the data processing module to achieve more complex motion recognition and other functions. For example, an acceleration sensor can be configured to collect acceleration during human body movement. Specifically, acceleration measurement can be mainly used for step counting and calorie calculation during user exercise, and can also be used to monitor the acceleration of the body in the three axes of X, Y, and Z during user exercise.

[0117] In some embodiments, the ECG sensor can be configured to collect ECG data during the user's exercise. The ECG sensor and the data processing module (for example, the first top data processing module 14121, the second top data processing module 14122) can be connected and communicated. The user's heart rate will change during exercise. For example, when the user is doing aerobic exercise or strength training, the length of the user's exercise time and / or the size of the exercise intensity can affect the user's heart rate. The ECG sensor can collect the user's ECG signal during exercise and pass the collected ECG signal to the data processing module. The data processing module performs data processing on the received ECG signal (or the data processing module passes the received ECG signal to the peripheral terminal, and the peripheral terminal performs data processing on the received ECG signal), and determines whether the user's heart rate is within the judgment standard. If it exceeds the judgment standard, the wearable device can alert the user through the feedback module. The judgment standard here can be trained in advance by the ECG data of professionals (for example, athletes, coaches, etc.) and a large number of ordinary people during exercise, and adjusted and adapted according to the user's information. Users can understand in real time whether their ECG status is normal based on the alerts from the feedback module, and adjust exercise time and / or exercise intensity in a timely manner.

[0118] In some embodiments, the breathing sensor can be configured to collect breathing signals during the user's exercise. The breathing sensor and the data processing module (for example, the first top data processing module 14121, the second top data processing module 1412) can be connected and communicated. During the exercise, the user's breathing speed and breathing frequency will change. For example, during the running process, the user's breathing speed will gradually increase as the user's running time passes and / or the running speed increases, and the breathing frequency will gradually increase as the user's running time passes and / or the running speed increases. The breathing sensor collects the user's breathing signals (such as breathing speed, breathing frequency, etc.) during the exercise process, and transmits the collected breathing signals to the data processing module. The data processing module performs data analysis on the received breathing signal (or the data processing module transmits the received breathing signal to the peripheral terminal, and the peripheral terminal performs data processing on the received breathing signal), and determines whether the breathing data during the user's running exercise is within the judgment standard. If it exceeds the judgment standard, the wearable device can alert the user through the feedback module. The judgment criteria here can be trained in advance by using the breathing data of professionals (e.g., athletes, coaches, etc.) and a large number of ordinary people during running, which are recorded in the wearable device, and adjusted and adapted according to the user's information. The user can understand in real time whether his or her running status (e.g., running speed, running time, etc.) is standard according to the warning of the feedback module, and adjust the running time and / or running speed in time.

[0119] In some embodiments, the temperature sensor can be configured to collect temperature signals during the user's exercise. The temperature sensor and the data processing module (for example, the first top data processing module 14121, the second top data processing module 14122, the first pants data processing module 14221, and the second pants data processing module 14222) can be connected and communicated. During the exercise, the user's body temperature will gradually increase. For example, when the user is doing aerobic exercise or strength training, the length of the user's exercise time and / or the size of the exercise intensity can affect the user's body temperature. The temperature sensor can collect temperature signals during the user's exercise and pass the collected temperature signals to the data processing module. The data processing module performs data processing on the received temperature signal (or the data processing module passes the received temperature signal to the peripheral terminal, and the peripheral terminal performs data processing on the received temperature signal), and determines whether the user's body temperature is within the judgment standard. If it exceeds the judgment standard, the wearable device can alert the user through the feedback module. The judgment standard here can be trained in advance by the temperature data of professionals (for example, athletes, coaches, etc.) and a large number of ordinary people during exercise, and adjusted and adapted according to the user's information. Users can understand in real time whether their temperature status is normal based on the warnings from the feedback module, and adjust the exercise time and / or exercise intensity in a timely manner.

[0120] In some embodiments, the humidity sensor can be configured to collect humidity signals during the user's exercise. The humidity sensor and the data processing module (for example, the first top data processing module 14121, the second top data processing module 14122, the first pants data processing module 14221, and the second pants data processing module 14222) can be connected and communicated. During the user's exercise, the body humidity will gradually increase. For example, when the user is doing aerobic exercise or strength training, the length of the user's exercise time and / or the size of the exercise intensity can affect the user's body humidity. The humidity sensor can collect humidity signals during the user's exercise and pass the collected humidity signals to the data processing module. The data processing module performs data processing on the received humidity data (or the data processing module passes the received humidity signal to the peripheral terminal, and the peripheral terminal performs data processing on the received humidity signal), and determines whether the user's body humidity is within the judgment standard. If it exceeds the judgment standard, the wearable device can alert the user through the feedback module. The judgment criteria here can be trained in advance by using humidity data of professionals (e.g., athletes, coaches, etc.) and a large number of ordinary people during exercise recorded in the wearable device, and adjusted and adapted according to the user's information. Users can understand in real time whether their humidity status is normal based on the warning of the feedback module, and adjust the exercise time and / or exercise intensity in time.

[0121] Fig.15 is an exemplary structural diagram of the wiring connection method of the upper wearable device shown in some embodiments of the present application. Fig.15 As shown, the upper wearable device 1500 may include a clothing base 1510, a first data processing module 1521, a second data processing module 1522, a first electromyographic sensor 1531, a second electromyographic sensor 1532, a temperature sensor 1541, a humidity sensor 1542, a first electrocardiographic sensor 1551, a second electrocardiographic sensor 1552, a connecting line 1561 (or a connecting line 1562, a connecting line 1571, a connecting line 1572, a connecting line 1581, a connecting line 1582, etc.), etc. Specifically, the first electromyographic sensor 1531 is connected to communicate with the first data processing module 1521 through the connecting line 1561. The second electromyographic sensor 1532 is connected to communicate with the second data processing module 1522 through the connecting line 1562. The temperature sensor 1541 is connected to communicate with the first data processing module 1521 through the connecting line 1571. The humidity sensor 1542 is connected to communicate with the second data processing module 1522 through the connecting line 1572. The first electrocardiogram sensor 1551 is connected to the first data processing module 1521 through a connection line 1581 for communication. The second electrocardiogram sensor 1552 is connected to the second data processing module 1522 through a connection line 1582 for communication.

[0122] In some embodiments, the left shoulder of the upper wearable device 1500 is provided with a first data processing module 1521, and the right shoulder is provided with a second data processing module 1522. The first data processing module 1521 and the second data processing module 1522 are respectively configured to receive motion data of the left and right sides of the user's body. On the one hand, this design can effectively share the routing lines and reasonably control the volume of a single data processing module (for example, the first data processing module 1521 and the second data processing module 1522). On the other hand, the design of respectively providing data processing modules on the left and right sides of the upper wearable device 1500 is a symmetrical design, which can effectively solve the user safety problems caused by asymmetrical design (for example, balance control of movements such as squats). On the other hand, the design of respectively providing data processing modules on the left and right sides of the upper wearable device 1500 can effectively avoid the presence of electronic devices such as circuits (for example, batteries, Bluetooth, amplifiers, etc.) on the user's chest and near major organs such as the heart, while improving the user's wearing comfort. In some embodiments, the design of respectively setting data processing modules on the left and right shoulders of the wearable upper device 1500 can reduce the difficulty of design and the weight of each data processing module, and can also effectively collect physiological signals near the chest (such as electrocardiogram signals, electromyography signals of the pectoralis major muscle, etc.).

[0123] In some embodiments, when there are many sensor modules on the upper wearable device 1500, the above wiring method can effectively separate the line layout, reduce the difficulty of wiring, and improve the design space. On the other hand, it can avoid large-angle wiring. In some embodiments, the wiring length in the wearable device will affect its signal-to-noise ratio. Specifically, the longer the wiring length, the greater the noise interference introduced. Fig.15 The wiring method can effectively shorten the wiring length, thereby reducing the noise signal collected by the sensor module and reducing the interference of noise. In some embodiments, the sensor modules are connected to the data processing module for communication. The wiring in the wearable device is relatively dense, and mutual interference will occur between the channels. Fig.15 The routing method can effectively increase the distance between each routing and reduce mutual interference between channels.

[0124] In some embodiments, when the user is exercising, most of the movements (for example, barbell bench press, dumbbell press, running, chest expansion exercises, etc.) require the participation of human limbs. The movement of both arms can drive the displacement of the wearable device, thereby causing the sensor module in the wearable device to displace, thereby reducing the signal acquisition quality (for example, electromyographic signals and electrocardiographic signals at the pectoralis major muscle position). Fig.16A : is an exemplary structural diagram of the elastic design of the underarm position of the upper wearable device according to some embodiments of the present application. Fig.16AAs shown, a first elastic design 1611 is provided at the left underarm position of the clothing base 1610 , and a second elastic design 1612 is provided at the right underarm position of the clothing base 1610 . Fig. 16B : is an exemplary structural diagram of the elastic design of the upper arm position of the upper wearable device shown in some embodiments of the present application. Fig. 16B As shown, a third elastic design 1621 is provided at the left upper arm position of the clothing base 1620, and a fourth elastic design 1622 is provided at the right upper arm position of the clothing base 1620. The third elastic design 1621 and the fourth elastic design 1622 are upper arm annular elastic designs. It should be noted that the setting positions of the elastic design may include but are not limited to the armpit position and the upper arm position. This embodiment only describes the armpit position and the upper arm position, and other human body positions (such as the elbow position, the shoulder position, etc.) are not described in detail here.

[0125] In some embodiments, elastic design may refer to the use of highly elastic and stretchable materials. The highly elastic and stretchable materials may include but are not limited to elastic fiber fabric materials, flexible polymer materials, elastic rubber rings, etc. In addition, the material used for elastic design may be a single elastic material or a combination of multiple different elastic materials. For example, the upper arm position of the wearable device (e.g., Fig. 16B The third elastic design 1621 or Fig. 16B The clothing base at the fourth elastic design 1622) can be made of elastic rubber material. When the user's upper arm is pulled, the highly elastic rubber material can stretch, thereby effectively avoiding the displacement of the wearable device. For another example, the armpit area of ​​the wearable device (for example, Fig.16A First elastic design 1611 or Fig.16A The clothing base at the second elastic design 1612) can be made of a combination of elastic fiber fabric inserts and nylon material (or polyester stretch material). Specifically, when the user stretches his arm, the armpit area of ​​the wearable device is pulled. The combination of elastic fiber fabric inserts and nylon material (or polyester stretch material) has a better stretch rate and recovery rate, which can effectively avoid the displacement of the wearable device.

[0126] In some embodiments, elastic design may also refer to structural design. Specifically, the wearable device may be placed near the upper arm of the human body (see Fig. 16BThe third elastic design 1621 and the fourth elastic design 1622) are designed with a wrinkled undulating structure. The wrinkled undulating structure protrudes in a three-dimensional ring shape relative to the wearable device itself, and the size of the protruding displacement can be determined according to the size of the pulling force during the movement. When the wrinkled undulating structure is pulled by the user's movement (for example, a barbell bench press) at the upper arm position, it can be stretched and contracted along the pulling direction, thereby effectively alleviating the displacement of the wearable device due to pulling, affecting the signal acquisition quality.

[0127] In some embodiments, the periphery of the electrode module may be elastically designed based on the tensile force analysis near the electrode. Fig.17A 1 is an exemplary structural diagram of the annular elastic design of the electrode module of the upper wearable device according to some embodiments of the present application. Fig.17A As shown, an annular elastic design 1720 (for example, using highly elastic stretchable materials, pleated design, etc.) is provided on the periphery of the electrode module 1710, which can reduce the pulling of the electrode module by the user during exercise in 360 degrees. For example, when a user wearing a sports device performs arm wrapping and stretching exercises, the electrode module 1710 on the chest and its vicinity will be pulled at multiple angles. In this case, an annular elastic design 1720 (for example, using highly elastic stretchable materials, pleated design, etc.) is provided on the periphery of the electrode module 1710, which can effectively avoid the displacement of the electrode module 1710 caused by the user pulling, and further reduce the influence of the user's movement on the signal acquisition module. Fig. 17B 1 is an exemplary structural diagram of a top wearable device electrode module with specific directional elastic design according to some embodiments of the present application. Fig. 17B As shown, an elastic design 1740 (for example, using a highly elastic stretchable material, a pleated design, etc.) is provided in one or more specific directions of the electrode module 1730 to reduce the pulling in one or more specific directions. For example, when a user wearing a sports device performs chest expansion exercises, the electrode module 1730 on the chest will be pulled on the side close to the direction of the ipsilateral arm. In this case, an elastic design 1740 (for example, using a highly elastic stretchable material, a pleated design, etc.) is provided on the chest electrode module 1730 close to the direction of the ipsilateral arm to effectively avoid the displacement of the electrode module 1730 due to the pulling of the user, and further reduce the influence of the user's movement on the signal acquisition module.

[0128] Fig.18 is an exemplary structural diagram of a hollow design of a wearable device according to some embodiments of the present application. Fig.18 As shown, the partial clothing base 1800 may include a first side end 1811, a second side end 1812, a third side end 1813, a fourth side end 1814, a hollow design clothing base 1820 ( Fig.18 Middle shaded area), conventional clothing base 1830 ( Fig.18 Here, the partial clothing base 1800 may be a structure of a partial area of ​​clothing, and the first side end 1811, the second side end 513, the third side end 1814 and the fourth side end 1814 may be connected to the clothing respectively. The first side end 1811 and the second side end 1812 are arranged opposite to each other, and the wearable device with hollow design may have better ductility than conventional wearable devices by pulling along the direction of the first side end 1811 and the second side end 1812. Fig.18 , wherein the third side end 1813 and the fourth side end 1814 are arranged opposite to each other, and when pulled along the direction of the third side end 1813 and the fourth side end 1814, the hollow structure becomes larger under the pulling, so that the wearable device with a hollow design can have better extensibility than a conventional wearable device. In some embodiments, when a user wearing a sports device performs chest expansion exercises, the clothing at the user's chest position is displaced due to the pulling of the action. A hollow structure is set around the chest of the wearable device, and the hollow structure can effectively weaken the displacement of the electrode relative to the skin caused by the pulling of the user's action, thereby effectively improving the signal acquisition quality at the user's chest position. Reference Fig.18 The hollow design method shown, on the one hand, can make clothing of the same material have better ductility, and can also effectively enhance the stretchability of clothing. On the other hand, it can make the clothing have better breathability and aesthetic advantages. On the other hand, the hollow design can avoid the splicing of different materials, and it can be easier to save costs in processing technology. It should be noted that the hollow structure can be set at multiple positions of the clothing base, and this application does not limit this. The shape of the partial clothing base 1800 and the hollow design clothing base 1820 is not limited to Fig.18 The rectangular shape shown in the figure can also be regular or irregular shapes such as triangle, circle, parallelogram, rhombus, etc. In addition, the side ends for connecting with clothing are not limited to the first side end 1811, the second side end 1812, the third side end 1813 and the fourth side end 1814 mentioned above, and can be adaptively adjusted according to the shape of part of the clothing base 1800.

[0129] In some embodiments, the clothing base of the wearable device can be designed with additional elasticity. This additional elasticity design can be achieved through processes such as 3D printing, and can be a strip of additional material attached to the clothing base, or it can be a material splicing and / or structural design of the clothing base itself. Relevant descriptions of clothing materials and structural designs can be found in Fig.16AIt can be found in , and this embodiment will not be repeated here. In some embodiments, local pressure is designed near the electrodes in the wearable device, which can effectively enhance the fit of the electrodes to the human body, while not increasing the pressure of the rest of the wearable device on the human body, and not affecting the wearing comfort of the user. For example, a pressure design is performed at the arm joint position of the wearable device. When the user is exercising, the arm position is pulled. In this case, the pressure design at the arm joint position can effectively reduce the displacement of the clothing base on the user's body. In some embodiments, local pressure is designed near the electrodes in the wearable device, which can also effectively enhance the consistency of the two electrodes on the electrode module. Specifically, the surface of the human body is an irregular curved surface, and the same electrode module is set in the clothing base to fit the surface of the human body and will also face different fitting pressures. In this case, the local pressure design near the electrodes in the wearable device can effectively adjust the fitting pressure balance of the two electrodes on the electrode module.

[0130] In some embodiments, external factors such as human body curves and human body movements may affect the electrode modules in the clothing base. In order to effectively avoid the influence of line switching, flexible to hard operations and other operations on electrode consistency, this embodiment provides a knife-shaped electrode. Fig.19A is an exemplary structural diagram of a knife-shaped electrode according to some embodiments of the present application. Fig.19A As shown, the blade-shaped electrode may include a first electrode portion 1910 (corresponding to Fig.19A The shaded part) and the second electrode part 1920 (corresponding to Fig.19AThe first electrode portion 1910 is connected to the second electrode portion 1920, wherein the first electrode portion 1910 is used to contact the human skin, and the second electrode portion 1920 is used to transfer the data line so as to transmit the electromyographic signal collected by the first electrode portion 1910. In some embodiments, the upper surface of the second electrode portion 1920 may not contact the user's skin. Further, the first electrode portion 1910 and the second electrode portion 1920 have a certain height difference. When the first electrode portion 1910 contacts the skin, there is a certain distance between the second electrode portion 1920 and the human skin. By transferring the data line at the second electrode portion 1920, the second electrode portion 1920 can be prevented from interfering with the collection of the electromyographic signal of the first electrode portion 1910. In some embodiments, part of the upper surface of the second electrode portion 1920 can contact the user's skin. In some embodiments, the lower surface of the first electrode portion 1910 and the lower surface of the second electrode portion 1920 may be on the same plane, and the thickness of the first electrode portion 1910 is greater than the thickness of the second electrode portion 1920, so that when the first electrode 1910 contacts the user's skin, there is a certain distance between the second electrode portion 1920 and the user's skin, and the second electrode portion 1920 does not contact the user's skin. In some embodiments, the lower surface of the first electrode portion 1910 and the lower surface of the second electrode portion 1920 may not be on the same plane. For example, the lower surface of the first electrode portion 1910 is located above the lower surface of the second electrode portion 1920. For another example, the lower surface of the second electrode portion 1920 may be located above the first electrode portion, but the upper surface of the second electrode portion 1920 is below the upper surface of the first electrode portion 1910, so that when the first electrode 1910 contacts the user's skin, there is a certain distance between the second electrode portion 1920 and the user's skin, and the second electrode portion 1920 does not contact the user's skin. Fig.19B is an exemplary cross-sectional view of a knife-shaped electrode according to some embodiments of the present application. Fig.19B As shown, for the convenience of explanation and description, only as an exemplary illustration, the knife-shaped electrode structure is applied to clothing, the lower surface of the first electrode part 1910 is connected to the first plane of the inner layer of the clothing, and the upper surface of the second electrode part 1920 is connected to the first plane, so that the second electrode part 1920 is located between the first plane and the second plane. The first plane and the second plane here can be the inner and outer sides of the clothing or other structures connected to the clothing. Among them, the first plane and the second plane are both insulating materials. For example, the insulating material can refer to polyester, cotton cloth, rubber, aramid fiber, etc., which is not limited in this embodiment.

[0131] In some embodiments, increasing the size of the electrode can effectively prevent the electrode from falling off due to user movement, while ensuring that the sensor can collect signals as much as possible. For the material and size of the knife-shaped electrode, please refer to other places in this application (for example, Figure 3 ) description.

[0132] In some embodiments, Fig.19A The second electrode portion 1920 in the device may be a region for switching the conducted signal away from the first electrode portion 1910. Most electrodes in wearable devices are flat, and the flat electrodes are cut and used directly for signal conduction, which will take up a relatively large space and have a large resistance in the signal conduction line, which is not conducive to long-distance signal transmission. In this case, through the knife-shaped structure design and the use of special materials (such as flexible materials, elastic materials, etc.), special processing techniques and special structures to make the conductive wire, the second electrode portion 1920 can be switched (for example, the conductive wire is electrically connected to the second electrode 1920), so that the electrode can achieve long-distance signal transmission.

[0133] In some embodiments, the electrodes may be designed to be non-slip. When the user is exercising, the electrodes may move and / or fall off due to the pulling of the movements, so the electrodes need to be fixed and designed to be non-slip. Fig.19B , the second electrode part 1920 passes through the vicinity of the first plane, and the second electrode part 1920 can be fixed for the first time. Before the second electrode part 1920 performs signal transfer, the second electrode part 1920 can be fixed for the second time. It should be noted that the fixing method here can be a physical connection such as bonding and welding, and the fixing position and fixing order can also be determined as needed, which is not limited in this embodiment. In some embodiments, a local pressure design can be performed near the knife-shaped electrode structure. The local pressure design near the knife-shaped electrode structure in the wearable device can effectively enhance the fit of the knife-shaped electrode structure to the human body. For example, a pressure design is performed at the arm joint position of the wearable device. When the user is exercising, the arm position is pulled. In this case, the pressure design at the arm joint position can effectively reduce the displacement of the clothing base on the user's body, thereby effectively avoiding the sliding of the knife-shaped electrode structure set at the human arm position. In some embodiments, silicone can be applied around the knife-shaped electrode structure to increase the friction between the knife-shaped electrode structure and the skin, thereby effectively avoiding the displacement of the knife-shaped electrode structure due to the pulling of the user's movement. In some embodiments, elastic design can be performed near the blade-shaped electrode structure. A detailed description of the elastic design can be found in Fig.17A , Fig. 17B In some embodiments, a hollow design may be performed near the knife-shaped electrode structure. A detailed description of the hollow design may be found in Fig.18 In some embodiments, an adsorption design can also be performed near the knife-shaped electrode structure. A detailed description of the adsorption design can be found in Fig.12 , Fig.13, and this embodiment will not be described in detail.

[0134] It should be noted that the electrode modules in the above embodiments (e.g., electrode module 100, electrode module 200, electrode module 300 and the electromyographic module in the wearable device) can not only be used for the collection of electromyographic signals, but also release current to stimulate specific parts of the human body to achieve corresponding prompting effects or massage and relaxation effects. For example, when a user is exercising, the wearable device can determine whether the user's fitness movements are standardized based on the human body movement data, and use the electrode module to release current to achieve the effect of prompting the user's exercise status.

[0135] It should be noted that different embodiments may produce different beneficial effects. In different embodiments, the beneficial effects that may be produced may be any one or a combination of the above, or any other beneficial effects that may be obtained.

[0136] The basic concepts have been described above. Obviously, for those skilled in the art, the above detailed disclosure is only for example and does not constitute a limitation of the present application. Although not explicitly stated herein, those skilled in the art may make various modifications, improvements and amendments to the present application. Such modifications, improvements and amendments are suggested in the present application, so such modifications, improvements and amendments still belong to the spirit and scope of the exemplary embodiments of the present application.

[0137] At the same time, the present application uses specific words to describe the embodiments of the present application. For example, "one embodiment", "an embodiment", and / or "some embodiments" refer to a certain feature, structure or characteristic related to at least one embodiment of the present application. Therefore, it should be emphasized and noted that "one embodiment" or "an embodiment" or "an alternative embodiment" mentioned twice or more in different positions in this specification does not necessarily refer to the same embodiment. In addition, some features, structures or characteristics in one or more embodiments of the present application can be appropriately combined.

[0138] In addition, unless explicitly stated in the claims, the order of the processing elements and sequences described in this application, the use of alphanumeric characters, or the use of other names are not intended to limit the order of the processes and methods of this application. Although the above disclosure discusses some invention embodiments that are currently considered useful through various examples, it should be understood that such details are only for illustrative purposes, and the attached claims are not limited to the disclosed embodiments. On the contrary, the claims are intended to cover all modifications and equivalent combinations that are consistent with the essence and scope of the embodiments of this application. For example, although the system components described above can be implemented by hardware devices, they can also be implemented only by software solutions, such as installing the described system on an existing server or mobile device.

[0139] Similarly, it should be noted that in order to simplify the description of the disclosure of this application and thus help understand one or more embodiments of the invention, in the above description of the embodiments of this application, multiple features are sometimes combined into one embodiment, figure or description thereof. However, this disclosure method does not mean that the features required by the object of this application are more than the features mentioned in the claims. In fact, the features of the embodiments are less than all the features of the single embodiment disclosed above.

[0140] In some embodiments, numbers describing the number of components and attributes are used. It should be understood that such numbers used in the description of the embodiments are modified by the modifiers "about", "approximately" or "substantially" in some examples. Unless otherwise specified, "about", "approximately" or "substantially" indicate that the numbers are allowed to vary by ±20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximate values, which may change according to the required features of individual embodiments. In some embodiments, the numerical parameters should take into account the specified significant digits and adopt the general method of retaining digits. Although the numerical domains and parameters used to confirm the breadth of their range in some embodiments of the present application are approximate values, in specific embodiments, the setting of such numerical values ​​is as accurate as possible within the feasible range.

[0141] Each patent, patent application, patent application disclosure, and other materials, such as articles, books, instructions, publications, documents, etc., cited in this application are hereby incorporated by reference in their entirety. Except for application history documents that are inconsistent with or conflicting with the content of this application, documents that limit the broadest scope of the claims of this application (currently or later attached to this application) are also excluded. It should be noted that if the descriptions, definitions, and / or use of terms in the attached materials of this application are inconsistent or conflicting with the content described in this application, the descriptions, definitions, and / or use of terms in this application shall prevail.

[0142] Finally, it should be understood that the embodiments described in this application are only used to illustrate the principles of the embodiments of the present application. Other variations may also fall within the scope of the present application. Therefore, as an example and not a limitation, the alternative configurations of the embodiments of the present application may be considered to be consistent with the teachings of the present application. Accordingly, the embodiments of the present application are not limited to the embodiments explicitly introduced and described in the present application.

Claims

1. A device for collecting and processing human electromyographic signals, characterized in that: The device comprises: An electrode module is configured to collect electromyographic signals of a human body; The electrode module comprises a base structure and at least two electrodes, wherein the at least two electrodes are arranged at intervals and disposed on the surface of the base structure; Wherein, the electrode module comprises a plurality of suction cup structures, and the plurality of suction cup structures are located on the surface of the at least two electrodes or the substrate structure; The suction cup structure is a three-dimensional structure, and the suction cup structure includes a hollow portion, and the hollow portion has an opening at one end of the suction cup structure for contacting with human skin; The suction cup structure also includes an intermediate structure, which is located in the hollow part of the suction cup structure, wherein a part of the intermediate structure is connected to the side wall of the suction cup structure where the hollow part is located, and the intermediate structure divides the hollow part of the suction cup structure into a plurality of interconnected spatial areas.

2. The device for collecting and processing human electromyographic signals according to claim 1, characterized in that: The at least two electrodes include a first electrode and a second electrode, and the first electrode and the second electrode are arranged in parallel and disposed on a surface of the base structure.

3. The device for collecting and processing human electromyographic signals according to claim 2, characterized in that: The at least two electrodes further include a reference electrode, and the first electrode, the reference electrode and the second electrode are sequentially arranged in parallel and disposed on the surface of the base structure.

4. The device for collecting and processing human electromyographic signals according to claim 2, characterized in that: The at least two electrodes further include a third electrode and a fourth electrode, and the third electrode and the fourth electrode are arranged in parallel and disposed on the surface of the base structure; The first electrode and the third electrode are arranged side by side, and the second electrode and the fourth electrode are arranged side by side.

5. The device for collecting and processing human electromyographic signals according to claim 1, characterized in that: The electrode module includes a plurality of protrusion structures, and the plurality of protrusion structures are located on the surface of the at least two electrodes or the base structure.

6. The device for collecting and processing human electromyographic signals according to claim 5, characterized in that: The protrusion structures are arranged in an array or randomly distributed on the surface of the at least two electrodes or the base structure.

7. The device for collecting and processing human electromyographic signals according to claim 5, characterized in that: The convex structure is hollow inside, and the hollow part of the convex structure is filled with a filler.

8. The device for collecting and processing human electromyographic signals according to claim 5, characterized in that: The height of the protruding structure is 0.5 mm to 10 mm.

9. The device for collecting and processing human electromyographic signals according to claim 1, characterized in that: The plurality of suction cup structures are arranged in an array or randomly distributed on the at least two electrodes or on the surface of the base structure.

10. The device for collecting and processing human electromyographic signals according to claim 1, characterized in that: The plurality of suction cup structures are distributed on the surface of the base structure around the at least two electrodes.

11. The device for collecting and processing human electromyographic signals according to claim 1, characterized in that: The electrode module may further include a plurality of bump structures, and the bump structures are located on the surface of the base structure or the at least two electrodes.

12. The device for collecting and processing human electromyographic signals according to claim 11, characterized in that: The height of the plurality of bump structures is 10 μm to 80 μm.

13. The device for collecting and processing human electromyographic signals according to claim 12, characterized in that: The distribution density of the plurality of bump structures may be 2 / 2.25 mm2 to 10 / 2.25 mm2.

14. The device for collecting and processing human electromyographic signals according to claim 1, characterized in that: The electrode module further includes a plurality of air holes, and the plurality of air holes are located on the electrode and / or the base structure.

15. A wearable device, characterized in that: The device comprises a top garment and trousers garment, wherein the top garment and the trousers garment at least comprise an electromyographic module for collecting electromyographic signals of a human body, and the electromyographic module comprises the electrode module as claimed in any one of claims 1 to 14.

16. The wearable device according to claim 15, characterized in that The upper garment comprises at least: At least one upper body sensor module, configured to collect upper body movement data of a human body; At least one upper body data processing module, configured to receive and process the upper body movement data; The upper garment base is configured to carry the at least one upper garment sensor module and the at least one upper garment data processing module.

17. The wearable device according to claim 16, characterized in that The at least one upper garment sensor module includes at least a first upper garment sensor module and a second upper garment sensor module, wherein the first upper garment sensor module is located on a left side of the upper garment base, and the second upper garment sensor module is located on a right side of the upper garment base.

18. The wearable device according to claim 17, characterized in that The first upper garment sensor module and the second upper garment sensor module at least include the electromyographic module, the electrocardiographic sensor, the respiration sensor, the temperature sensor, the humidity sensor, the inertial sensor, the acid-base sensor, and the sound wave transducer.

19. The wearable device according to claim 18, characterized in that The inertial sensor is located in the garment processing module.

20. The wearable device according to claim 17, characterized in that The at least one upper garment processing module comprises at least a first upper garment processing module and a second upper garment processing module; wherein, The first upper garment processing module is located at the left shoulder of the upper garment base, and the first upper garment processing module is communicatively connected with the first upper garment sensor module; The second top processing module is located at the right shoulder of the top garment base, and the second top processing module is communicatively connected with the second top sensor module.

21. The wearable device according to claim 20, characterized in that The first upper garment processing module and the second upper garment processing module are in a master-slave relationship or a parallel relationship.

22. The wearable device according to claim 15, characterized in that The trousers garment at least comprises: At least one pants sensor module, configured to collect lower body movement data; At least one pants data processing module, configured to receive and process the lower body movement data; A trousers garment substrate is configured to carry the at least one trousers sensor module and the at least one trousers data processing module.

23. The wearable device according to claim 22, characterized in that The at least one trousers sensor module includes at least a first trousers sensor module and a second trousers sensor module, wherein the first trousers sensor module is located on a left side of the trousers garment base, and the second trousers sensor module is located on a right side of the trousers garment base.

24. The wearable device according to claim 23, characterized in that The first trousers sensor module and the second trousers sensor module at least include the electromyographic module, the electrocardiographic sensor, the breathing sensor, the temperature sensor, the humidity sensor, the inertial sensor, the acid-base sensor, and the sound wave transducer.

25. The wearable device according to claim 23, characterized in that The at least one trouser processing module comprises at least a first trouser processing module and a second trouser processing module; wherein, The first trousers processing module is located at the left side of the left leg of the trousers garment base, and the first trousers processing module is communicatively connected with the first trousers sensor module; The second trousers processing module is located at the right side of the right leg of the trousers garment base, and the second trousers processing module is communicatively connected with the second trousers sensor module.

26. The wearable device according to claim 25, characterized in that The first trousers processing module and the second trousers processing module are in a master-slave relationship or a parallel relationship.

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