Epidermal sensor for multiple monitoring of human motion signals and method of making the same

Abstract

The present application provides a kind of epidermis sensor for human motion signal multiple monitoring, including porous elastomer substrate, first electrode and second electrode being arranged in both ends of porous elastomer substrate, half portion of porous elastomer substrate is deposited with negative material, half portion of porous elastomer substrate is deposited with positive material, negative material and positive material are located in hole, first electrode and negative material form first rubbing pair, second electrode and positive material form second rubbing pair;Potential difference generated between first electrode and second electrode is used to measure electromyographic signal, induced potential between negative material and first electrode, positive material and second electrode generates, and induced potential is used to measure triboelectric signal;The present application can reflect electromyographic signal and triboelectric signal of muscle movement state simultaneously, and the movement of muscle can be fully reflected;Sensor is in the form of film as a whole, can be directly attached to the surface of human muscle, avoid restraint and aeration problem.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of human motion monitoring, in particular to a skin sensor for multi-monitoring of human motion signals and a preparation method thereof. BACKGROUND

[0002] In today's high-speed development of microelectronics and material technology, a large number of new microelectronic devices with multiple functions and high integration are being developed, and they show an unprecedented application prospect in various fields of people's daily life. With the gradual enhancement of health awareness, more and more people begin to pay attention to their own health conditions of exercise. The monitoring of human motion signals is of great significance for scientific and reasonable fitness and rehabilitation training. However, the traditional motion monitoring equipment has the problems of insufficient flexibility, insufficient comfort, and single signal acquisition which is difficult to comprehensively detect the human motion condition. In order to solve these problems, it is of great significance to develop a wearable skin sensor with multiple sensing principles. SUMMARY

[0003] The main purpose of the present application is to overcome the above-mentioned shortcomings and deficiencies of the prior art, and to provide a skin sensor for multi-monitoring of human motion signals.

[0004] A skin sensor for multi-monitoring of human motion signals, comprising a porous elastomer substrate, a first electrode and a second electrode arranged at both ends of the porous elastomer substrate, the porous elastomer substrate is a porous hole film, one half of the porous elastomer substrate provided with the first electrode is deposited with a negative material, one half of the porous elastomer substrate provided with the second electrode is deposited with a positive material, the negative material and the positive material are located in the hole, the first electrode and the negative material form a first friction pair, and the second electrode and the positive material form a second friction pair; when the muscle relaxes or contracts, the potential difference generated between the first electrode and the second electrode is used to measure the electromyographic signal, and the induced potential generated between the negative material and the first electrode and between the positive material and the second electrode is used to measure the triboelectric signal.

[0005] The skin sensor has two sensing principles, one is to measure the electromyographic signal through the electrode, and the other is to measure the muscle motion signal based on the triboelectric principle, i.e. the triboelectric signal. The electromyographic signal can distinguish the movement of the muscle under different forces, and the triboelectric signal can distinguish the movement of the muscle under different amplitudes. The present application combines the two signals and applies them to the same sensor, which can more fully reflect the movement of the muscle. At the same time, the skin sensor is in the form of a whole film, which can be directly attached to the surface of the human muscle, is more comfortable than other sensors, and avoids the problems of restraint and poor air permeability.

[0006] In an embodiment of one of the embodiments, the porous elastomer substrate is rectangular, and the porous elastomer substrate is a porous sponge-like elastomer.

[0007] In an embodiment of one of the embodiments, the elastomer is an elastic material such as polydimethylsiloxane, fluorinated silicone rubber, polyurethane, hydrogenated styrene-butadiene block copolymer, etc.

[0008] In an embodiment of one of the embodiments, the negative material can be an electron-donating material such as polytetrafluoroethylene, polyvinylidene fluoride, polyvinyl chloride, polyimide, etc.

[0009] In an embodiment of one of the embodiments, the positive material can be a nano-gold particle, nylon, or ethyl cellulose, and the elastomer is polydimethylsiloxane, fluorinated silicone rubber, polyurethane, hydrogenated styrene-butadiene block copolymer, etc.

[0010] In an embodiment of one of the embodiments, the two short sides of the skin sensor are attached to the skin by medical tape or double-sided tape.

[0011] In an embodiment of one of the embodiments, the first electrode and the second electrode are in the form of a strip, and the first electrode and the second electrode are a flexible stretchable conductive composite material.

[0012] In an embodiment of one of the embodiments, the flexible stretchable conductive composite material is a carbon fiber / polymer composite material, a conductive fiber / elastomer composite material, or a conductive polymer / elastomer composite material.

[0013] In an embodiment of one of the embodiments, when the muscle contracts, an action potential is generated and propagates along the muscle direction, sequentially passing through the first electrode and the second electrode, so that a potential difference is generated between the two electrodes, and the frequency of the electromyographic signal formed by the superposition of multiple action potentials is in the range of 50-150 Hz. When the muscle moves, the friction pairs in the pores of the porous elastomer substrate are separated after being in contact under the action of external force, the negative material is negatively charged, and the positive material is positively charged. These pores collectively generate an induced potential at the first electrode and the second electrode. When the muscle contracts, the distance between the negative material and the first electrode and the distance between the positive material and the second electrode decrease, and the induced potential decreases; when the muscle relaxes, the distance between the negative material and the first electrode and the distance between the positive material and the second electrode increase, and the induced potential increases. These changes in induced potential are the triboelectric signal, which reflects the movement state of the muscle, and the frequency of the triboelectric signal is below 10 Hz. The electromyographic signal and the triboelectric signal are separated by a filter.

[0014] In an embodiment of one of the embodiments, the first electrode and the second electrode are coated with conductive paste or conductive gel, and the purpose of the conductive paste or conductive gel is to reduce the contact impedance of the first electrode and the second electrode with the skin.

[0015] A method for preparing an epidermal sensor for multiple monitoring of human motion signals, comprising the following steps:

[0016] Step 1: Take a polyvinyl alcohol aqueous solution with a mass fraction of 5%-15%, coat it on a clean glass sheet, then place the glass sheet on a spin coater at a speed of 200-500 rpm for 1-3 minutes, and then place the glass sheet on a hot plate and heat it at 75-95°C for 25-35 minutes to obtain a polyvinyl alcohol layer;

[0017] Step 2: Place a mask on the polyvinyl alcohol layer, then use a scraper to scrape the conductive composite paste and make it deposit on the polyvinyl alcohol layer through the mask, and then peel off the mask to obtain a patterned conductive composite layer as an electrode;

[0018] Step 3: Mix 5g of liquid elastomer with 10g of soluble particles and coat them on the polyvinyl alcohol layer;

[0019] Step 4: Place the glass sheet in an oven and heat it at 100-130°C for 1.5-2.5 hours to completely cure the elastomer and the conductive composite material;

[0020] Step 5: Place the glass sheet in water and heat it at 80-95°C for 7-10 hours to completely dissolve the soluble particles in the elastomer, obtaining a porous elastomer substrate, and at the same time the polyvinyl alcohol layer is also dissolved in water, and the sample is obtained by peeling off the glass sheet;

[0021] Step 6: Divide the porous elastomer substrate into two halves with the midpoint of the long side as the boundary, immerse the lower half in a negative electric material solution for 25-40 minutes, then take it out and place it in a constant temperature drying oven and heat it at a temperature of 65-85°C for 1.5-2.5 hours to preliminarily slowly evaporate the solvent in the negative electric material solution, and then place it on a hot plate and heat it at a temperature of 110-130°C for 25-40 minutes to completely remove the residual solvent in the negative electric material;

[0022] Step 7: Immerse the other half of the porous elastomer substrate in a positive electric material solution for 25-40 minutes, then take it out and place it in a constant temperature drying oven and heat it at a temperature of 65-85°C for 1.5-2.5 hours to preliminarily slowly evaporate the solvent in the positive electric material, and then place it on a hot plate and heat it at a temperature of 110-130°C for 25-40 minutes to completely remove the residual solvent in the positive electric material, and the sensor manufacturing is completed;

[0023] In an implementation of one of the embodiments, in step 3, the soluble particles are sucrose particles, salt particles, sodium carbonate particles, sodium bicarbonate particles or citric acid particles. Preferably, the soluble particles are sucrose particles.

[0024] In an implementation of one of the embodiments, in step 6, the negative material solution is selected from a polytetrafluoroethylene emulsion, wherein the mass fraction of the polytetrafluoroethylene is 60%.

[0025] In an implementation of one of the embodiments, in step 7, the positive material solution is selected from a nano-gold colloid, wherein the content of the nano-gold particles is 0.2 mg / mL, and the particle size of the nano-gold particles is less than 20 nm.

[0026] When the human body moves, the epidermal sensor of the present application is attached to the surface of the human muscle, and the electromyographic signal and the triboelectric signal jointly act to form an alternating pulse signal output in the electrode. The muscle force and the movement amplitude are different under different movement states, and the signal amplitude measured is different, so that the muscle force and the movement amplitude can be distinguished, and the muscle movement can be more comprehensively monitored. Compared with the prior art, the epidermal sensor provided by the present application has the following beneficial effects:

[0027] 1. Multifunctional, compared with the single signal acquisition of the traditional sensor, it is difficult to comprehensively detect the human movement condition, the epidermal sensor of the present application can analyze, weight and integrate multiple signals, and can obtain more comprehensive and accurate human movement signals;

[0028] 2. Good wearability, the epidermal sensor in the present application is made of flexible material and is in the form of a film, which can be well attached to the human skin, and the sensor is transferred from the human hand to the specific forearm muscle of the human body, which eliminates the restriction on the normal activity of the human hand, and the porous elastomer substrate has good flexibility and air permeability, so that the epidermal sensor of the present application has good wearability and comfort;

[0029] 3. Non-invasive, compared with other monitoring methods, the epidermal sensor does not need to penetrate the skin or enter the human body, and does not need surgical operation, which can reduce the side effects such as infection and pain;

[0030] 4. High sensitivity. The epidermal sensor of the present application has high precision and can accurately monitor the weak muscle movement signal of the human body. BRIEF DESCRIPTION OF DRAWINGS

[0031] Figure 1 A schematic diagram of the epidermal sensor for human movement signal multiple monitoring of the present application;

[0032] Figure 2Potential sensing diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application;

[0033] Figure 3 Structure diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application;

[0034] Figure 4 Structure diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application; Figure 3 Structure diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application;

[0035] Figure 5 Structure diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application;

[0036] Figure 6 Signal diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application under different gripping forces;

[0037] Figure 7 Signal diagram of the epidermal sensor for multiple monitoring of human motion signals of the present application under different gripping amplitudes;

[0038] Figure 8 Preparation method of the epidermal sensor for multiple monitoring of human motion signals of the present application. DETAILED DESCRIPTION

[0039] Embodiments of the present application are described in detail below, examples of which are shown in the accompanying drawings, wherein the same or similar reference signs represent the same or similar elements or elements having the same or similar functions throughout. The embodiments described below by referring to the accompanying drawings are exemplary, only for explaining the present application, and cannot be understood as a limitation of the present application.

[0040] In the description of the present application, it should be understood that the terms "center", "longitudinal", "transverse", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential" and the like indicate the orientation or positional relationship based on the orientation or positional relationship shown in the drawings, and are only for the convenience of describing the present application and simplifying the description, and therefore cannot be understood as indicating or implying that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore cannot be understood as a limitation of the present application.

[0041] In addition, the terms "first", "second", "third", etc. are used only for descriptive purposes and do not connote or imply any relative importance or any meaning pertaining to the quantity of the features being described. Thus, a feature defined with "first", "second", etc. can include one or more of the features implicitly or explicitly. In the description of the present application, the meaning of "a plurality" is two or more, unless explicitly specified otherwise.

[0042] In the present application, unless specifically defined otherwise, the terms "mounting", "connecting", "connecting", "fixing" and the like should be interpreted broadly, for example, it can be fixed connection, or detachable connection, or integrated; it can be mechanical connection, or electrical connection; it can be directly connected, or indirectly connected through intermediate media, or the internal communication of two elements or the interaction relationship between two elements. For those skilled in the art, the specific meaning of the above terms in the present application can be understood according to the specific circumstances.

[0043] In the present application, unless specifically defined otherwise, the first feature is "on" or "under" the second feature, which can be direct contact between the first and second features, or indirect contact between the first and second features through intermediate media. Moreover, the first feature "above", "above" and "above" the second feature can be directly above or obliquely above the first feature, or only indicate that the horizontal height of the first feature is higher than that of the second feature. The first feature "below", "below" and "below" the second feature can be directly below or obliquely below the first feature, or only indicate that the horizontal height of the first feature is less than that of the second feature.

[0044] The present application provides a kind of for human motion signal multiple monitoring epidermal sensor, including porous elastomer substrate, first electrode and second electrode being arranged in the both ends of the porous elastomer substrate, the porous elastomer substrate is porous hole film, the half portion of the porous elastomer substrate with the first electrode is deposited with negative material, the half portion of the porous elastomer substrate with the second electrode is deposited with positive material, the negative material and positive material are located in hole, the first electrode and the negative material form first rubbing pair, the second electrode and the positive material form second rubbing pair;When muscle relaxes or contracts, the potential difference generated between the first electrode and the second electrode is used to measure electromyogram, the negative material and the first electrode, the positive material and the second electrode generate induced potential, and induced potential is used to measure triboelectric signal.

[0045] The epidermal sensor can simultaneously measure the myoelectric signal and the triboelectric signal that can reflect the muscle movement state, and can more fully reflect the muscle movement. Meanwhile, the epidermal sensor is in a whole film shape, can be directly attached to the muscle surface of the human body, is more comfortable than other sensors, and avoids the problems of restraint and air impermeability.

[0046] Embodiment one

[0047] Please refer to Figures 1 to 5 The present application provides an epidermal sensor for multiple monitoring of human motion signals, comprising a porous elastomer substrate 1, a first electrode 2 and a second electrode 3 arranged at both ends of the porous elastomer substrate 1, the porous elastomer substrate 1 is in a porous film shape, one half of the porous elastomer substrate 1 provided with the first electrode 2 is deposited with a negative material 4, in the embodiment, the negative material 4 is polytetrafluoroethylene, one half of the porous elastomer substrate 1 provided with the second electrode 3 is deposited with a positive material 5, the positive material 5 is nano gold particles, the negative material 4 and the positive material 5 are both located in the pores of the porous elastomer substrate 1, the first electrode 2 and the negative material 4 form a first triboelectric pair, and the second electrode 3 and the positive material 5 form a second triboelectric pair.

[0048] When the human motion muscle is relaxed or contracted, the potential difference between the first electrode 2 and the second electrode 3 is used to measure the myoelectric signal, and the induced potential between the negative material 4 and the first electrode 2 and the positive material 5 and the second electrode 3 is generated, and the induced potential is used to measure the triboelectric signal.

[0049] The epidermal sensor has two sensing principles, one is to measure the myoelectric signal through the first electrode 2 and the second electrode 3, and the other is to measure the muscle movement signal based on the triboelectric principle, i.e. the triboelectric signal. The myoelectric signal can distinguish the movement of the muscle under different forces, and the triboelectric signal can distinguish the movement of the muscle under different amplitudes, and the present application combines the two signals and applies them to the same sensor, which can more fully reflect the movement of the muscle. Meanwhile, the epidermal sensor is in a whole film shape, can be directly attached to the muscle surface of the human body, is more comfortable than other sensors, and avoids the problems of restraint and air impermeability.

[0050] More specifically, please refer to Figure 3, the porous elastomer base 1 is rectangular, the porous elastomer base 1 is a porous sponge-like elastomer 11, and the elastomer 11 is polydimethylsiloxane. In use, the epidermal sensor is attached to the human epidermis near the muscle belly, the electrode side is in contact with the human skin, the long side is along the muscle direction, and the short side is perpendicular to the muscle direction. In use, the two short sides of the epidermal sensor are attached to the skin by medical tape or double-sided tape. More specifically, the first electrode 2 and the second electrode 3 are coated with conductive paste or conductive gel, and the purpose of setting the conductive paste or conductive gel is to reduce the contact impedance of the first electrode 2 and the second electrode 3 with the skin.

[0051] More specifically, the first electrode 2 and the second electrode 3 are in the form of a strip, and the first electrode 2 and the second electrode 3 are flexible stretchable conductive composite materials. The flexible stretchable conductive composite material is a self-carbon fiber / polymer composite material, a conductive fiber / elastic material composite material, or a conductive polymer / elastic material composite material.

[0052] More specifically, please refer to Figure 2 When the muscle contracts, an action potential is generated and propagates along the muscle direction, sequentially passing through the first electrode 2 and the second electrode 3, so that a potential difference is generated between the two electrodes, and the frequency of the electromyographic signal formed by the superposition of multiple action potentials is in the range of 50-150 Hz. When the muscle moves, the frictional pairs in the pores of the porous elastomer base 1 are separated under the action of external force, the negative material 4 is negatively charged, and the positive material 5 is positively charged, and these pores collectively generate an induced potential at the first electrode 2 and the second electrode 3. When the muscle contracts, the distance between the negative material 4 and the positive material 5 decreases, and the induced potential decreases; when the muscle relaxes, the distance between the negative material 4 and the first electrode 2 and the distance between the positive material 5 and the second electrode 3 increase, and the induced potential increases. These changing induced potentials are triboelectric signals, which reflect the movement state of the muscle, and the frequency of the triboelectric signal is below 10 Hz. The electromyographic signal and the triboelectric signal are separated by a filter.

[0053] The main component of the electromyographic signal is in the range of 50-150 Hz, and the frequency of the triboelectric signal is below 10 Hz, so they can be separated by a filter. The electromyographic signal can distinguish the movement of the muscle under different forces (the greater the muscle force, the greater the electromyographic signal), and the triboelectric signal can distinguish the movement of the muscle under different amplitudes (the greater the muscle movement amplitude, the greater the triboelectric signal). The combination of the two signals can more fully reflect the movement of the muscle.

[0054] Please refer to Figure 6 , Figure 6 The signal graph measured by the sensor provided by the present application under different gripping forces, from Figure 6As can be seen, under different gripping forces, the amplitude of the triboelectric signal remains basically unchanged, while the amplitude of the electromyographic signal changes significantly, and the greater the gripping force, the greater the amplitude of the electromyographic signal.

[0055] Please see Figure 7 , Figure 7 The signal graphs obtained by the sensor provided by this invention under different gripping amplitudes are from... Figure 7 As can be seen, the amplitude of the electromyographic signal remains basically unchanged under different gripping ranges, while the amplitude of the triboelectric signal changes significantly, and the larger the gripping range, the larger the amplitude of the triboelectric signal.

[0056] Example 2

[0057] Please see Figure 8 The present invention discloses a method for preparing an epidermal sensor for multiple monitoring of human motion signals, comprising the following steps:

[0058] Step 1: Take a 5%-15% polyvinyl alcohol aqueous solution 7 and coat it onto a clean glass slide 6. Then place the glass slide 6 on a spin coater and spin coat it at a speed of 200-500 rpm for 1-3 minutes. After that, place the glass slide 6 on a hot plate and heat it at 75-95℃ for 25-35 minutes to obtain a polyvinyl alcohol layer.

[0059] Preferably, the polyvinyl alcohol aqueous solution 7 has a mass fraction of 8%-12%, and the glass slide 6 is spin-coated at a speed of 250-350 rpm for 1.5-2.5 minutes, followed by heating at 75-85°C for 25-30 minutes. More preferably, the polyvinyl alcohol aqueous solution 7 has a mass fraction of 10%, is spin-coated at a speed of 300 rpm for 2 minutes, and then heated at 80°C for 30 minutes.

[0060] Step 2: Apply mask 8 to the polyvinyl alcohol layer, then use scraper 9 to scrape the paste-like conductive composite material 10, allowing it to be deposited on the polyvinyl alcohol layer through the mask. After that, peel off the mask to obtain a patterned conductive composite material layer, which serves as an electrode.

[0061] Step 3: Mix 5-10g of liquid elastomer 11 with 10-20g of soluble particles 12 and coat the mixture onto the polyvinyl alcohol layer; preferably, 5g of liquid elastomer 11 is mixed with 10g of soluble particles 12. The mass ratio of prepolymer to curing agent in the elastomer 11 is 10:1.

[0062] Step 4: Place the glass slide 6 in an oven and heat it at 100-130°C for 1.5-2.5 hours to completely cure the elastomer 11 and the conductive composite material layer; preferably, the curing is carried out at 120°C for 2 hours.

[0063] Step 5, put the glass sheet 6 into water 13, heat for 7-10 hours at 80-95℃, so that the soluble particles 12 in the elastomer 11 are completely dissolved, and the porous elastomer substrate 1 is obtained, at the same time, the polyvinyl alcohol layer is dissolved in water and peeled off from the glass sheet; preferably, put the glass sheet 6 into water 13, heat for 8 hours at 90℃.

[0064] Step 6, immerse the lower half of the porous elastomer substrate 1 into the negative material solution 14, soak for 25-40 minutes, then take it out and put it into a constant temperature drying oven, heat for 1.5-2.5 hours at 65-85℃, so that the solvent in the negative material solution 14 is preliminarily and slowly evaporated, then put it on a hot plate and heat for 25-40 minutes at 110-130℃, so that the residual solvent in the negative material is completely removed, and the negative material deposition layer 4 is obtained; preferably, soak for 30 minutes, heat for 2 hours at 70℃, so that the solvent in the negative material solution 14 is preliminarily and slowly evaporated, then put it on a hot plate and heat for 30 minutes at 120℃.

[0065] Step 7, immerse the other half of the porous elastomer substrate 1 into the positive material solution 15, soak for 25-40 minutes, then take it out and put it into a constant temperature drying oven, heat for 1.5-2.5 hours at 65-85℃, so that the solvent in the positive material solution 15 is preliminarily and slowly evaporated, then put it on a hot plate and heat for 25-40 minutes at 110-130℃, so that the residual solvent in the positive material solution 15 is completely removed, and the positive material deposition layer 5 is obtained, and the sensor manufacturing is completed; preferably, soak for 30 minutes, then take it out and put it into a constant temperature drying oven, heat for 2 hours at 70℃, so that the solvent in the positive material solution 15 is preliminarily and slowly evaporated, then put it on a hot plate and heat for 30 minutes at 120℃.

[0066] In an embodiment of one of the embodiments, the soluble particles in step 3 are sucrose particles.

[0067] In an embodiment of one of the embodiments, the negative material solution 14 in step 6 is a polytetrafluoroethylene emulsion, and the mass fraction of polytetrafluoroethylene is 60%.

[0068] In an embodiment of one of the embodiments, the positive material solution 15 in step 7 is a nano-gold colloid, and the content of nano-gold particles is 0.2 mg / mL, and the particle size of nano-gold particles is less than 20 nm.

[0069] When the human body moves, the epidermal sensor of the application is attached to the surface of the human muscle, and the electromyographic signal and the triboelectric signal jointly act to form an alternating pulse signal output in the electrode, and the muscle force and the movement amplitude of the muscle are different in different movement states, and the signal amplitude measured is different, so that the muscle force and the movement amplitude can be distinguished, and the muscle movement can be more comprehensively monitored.

[0070] In view of the problem that common single-signal sensor is difficult to comprehensively detect the human movement state, the multi-sensing principle can analyze, weight and integrate multiple signals to obtain more comprehensive and accurate human movement signals. Secondly, the epidermal sensor is a sensor that can be directly attached to the skin to measure physiological signals, which is more comfortable than other sensors and avoids the problems of restraint and poor air permeability. At the same time, the epidermal sensor can effectively record the human muscle movement state, and can also accurately record physiological indicators such as heart rate and respiration, so it has a broad application prospect in movement monitoring. The combination of these technologies provides a technical basis for developing a multi-sensing principle epidermal sensor for human movement signal detection. In practical application, the technology can realize efficient, accurate and convenient human movement monitoring, which has important significance for the majority of sports enthusiasts and rehabilitation patients.

[0071] The technical features of the above-described embodiments can be combined arbitrarily, and to make the description concise, all possible combinations of the technical features in the above-described embodiments are not described, however, as long as the combinations of the technical features do not exist contradictory, they should be considered as the scope of the present application.

[0072] The above-described embodiments only express several embodiments of the application, and the description is more specific and detailed, but it should not be understood as a limitation on the scope of the patent. It should be pointed out that for ordinary skilled in the art, without departing from the concept of the present application, a number of modifications and improvements can be made, which are within the scope of the present application. Therefore, the protection scope of the patent of the present application should be subject to the appended claims.

Claims

1. An epidermal sensor for multiple monitoring of human motion signals, characterized in that, The application relates to a porous elastomer substrate, a first electrode and a second electrode arranged at two ends of the porous elastomer substrate, wherein the porous elastomer substrate is in a porous hole film shape, a half part of the porous elastomer substrate provided with the first electrode is deposited with a negative material, a half part of the porous elastomer substrate provided with the second electrode is deposited with a positive material, the negative material and the positive material are located in the holes, the first electrode and the negative material form a first rubbing pair, the second electrode and the positive material form a second rubbing pair; when a muscle relaxes or contracts, a potential difference between the first electrode and the second electrode is used to measure a muscle electric signal, an induced potential between the negative material and the first electrode and between the positive material and the second electrode is used to measure a triboelectric signal; the frequency of the muscle electric signal is in the range of 50-150 Hz, the frequency of the triboelectric signal is below 10 Hz, and the muscle electric signal and the triboelectric signal are separated through a filter.

2. The epidermal sensor for multiple monitoring of human motion signals according to claim 1, characterized in that: The negative material is selected from polytetrafluoroethylene, polyvinylidene fluoride, polyvinyl chloride or polyimide.

3. The epidermal sensor for multiple monitoring of human motion signals according to claim 1, wherein: The positive material is selected from nano gold particles, nylon or ethyl cellulose.

4. The epidermal sensor for multiple monitoring of human motion signals according to claim 1, wherein: The porous elastomer substrate is in a rectangular shape, and the porous elastomer substrate is a porous hole sponge-shaped elastomer.

5. The epidermal sensor for multiple monitoring of human motion signals according to claim 4, characterized in that: The elastomer is selected from polydimethylsiloxane, fluorinated silicone rubber, polyurethane or hydrogenated styrene-butadiene block copolymer.

6. The epidermal sensor for multiple monitoring of human motion signals according to claim 1, wherein: The first electrode and the second electrode are in a strip shape, and the first electrode and the second electrode are flexible stretchable conductive composite materials.

7. The epidermal sensor for multiple monitoring of human motion signals according to claim 6, characterized in that: The flexible stretchable conductive composite material is selected from carbon fiber / polymer composite material, conductive fiber / elastomer composite material and conductive polymer / elastomer composite material.

8. A method for fabricating an epidermal sensor for multiplexed monitoring of human motion signals, characterized by: The application further discloses a preparation method of the electrode. Step 1: a polyvinyl alcohol aqueous solution with a mass fraction of 5%-15% is coated on a clean glass sheet, then the glass sheet is placed on a spin coater, and spin coating is carried out at a rotating speed of 200-500 rpm for 1-3 minutes, and then the glass sheet is placed on a hot plate and heated at 75-95 DEG C for 25-35 minutes to obtain a polyvinyl alcohol layer; Step 2: a mask is attached to the polyvinyl alcohol layer, then a paste-like conductive composite material is scraped by a scraper to be deposited on the polyvinyl alcohol layer through the mask, and then the mask is peeled off to obtain a patterned conductive composite material layer as an electrode; Step 3: 5g of liquid elastomer is mixed with 10g of soluble particles and coated on the polyvinyl alcohol layer; Step 4: the glass sheet is placed in an oven and heated at 100-130 DEG C for 1.5-2.5 hours to completely cure the elastomer and the conductive composite material; Step 5: the glass sheet is placed in water and heated at 80-95 DEG C for 7-10 hours to completely dissolve the soluble particles in the elastomer, so as to obtain a porous elastomer substrate, and meanwhile the polyvinyl alcohol layer is also dissolved in water, and the sample is obtained by peeling off the glass sheet. Step 6, the porous elastomer substrate is divided into two halves with the midpoint of the long side as the boundary, the lower half is immersed in the negative material solution with a mass fraction of 40% to 60% for 25-40 minutes, then taken out and placed in a constant temperature drying oven, heated at a temperature of 65-85 ℃ for 1.5-2.5 h, so that the solvent in the negative material solution is preliminarily and slowly evaporated, then placed on a hot plate and heated at a temperature of 110-130 ℃ for 25-40 min to completely remove the residual solvent in the negative material; Step 7, the other half of the porous elastomer substrate is immersed in the positive material solution for 25-40 minutes, then taken out and placed in a constant temperature drying oven, heated at a temperature of 65-85 ℃ for 1.5-2.5 h, so that the solvent in the positive material solution is preliminarily and slowly evaporated, then placed on a hot plate and heated at a temperature of 110-130 ℃ for 25-40 min to completely remove the residual solvent in the positive material, and the sensor manufacturing is completed.

9. The method of claim 8, wherein the method further comprises: In the step 3 and step 5, the soluble particles are selected from sucrose particles, salt particles, sodium carbonate particles, sodium bicarbonate particles or citric acid particles.

Images