Flexible conductive patch, manufacturing method, storage box, and wearable device

Abstract

The present disclosure provides a flexible conductive patch, a manufacturing method, a storage box, and a wearable device, and relates to the technical field of physiological signal acquisition. The flexible conductive patch involved in the present disclosure is configured to be attached between an electrode and a biological tissue so as to transmit an electric signal from the biological tissue to the electrode. The wearable device of the present disclosure comprises: at least two electrodes configured to acquire the electric signal from the biological tissue; a wearable structure configured to carry the at least two electrodes, wherein the at least two electrodes are distributed spaced apart from each other on the wearable structure; and at least one flexible conductive patch, wherein the flexible conductive patch is configured to be detachably attached to at least one electrode to transmit the electric signal from the biological tissue to the electrode.

Description

A flexible conductive sheet, a manufacturing method, a storage box, and a wearable device. Technical Field

[0001] This application relates to the field of physiological signal acquisition technology, and in particular to a flexible conductive sheet, a manufacturing method, a storage box, and a wearable device. Background Technology

[0002] With the development of disease diagnostic technology and increased public awareness of health, the demand for monitoring physiological signals is growing. For example, electrocardiogram (ECG) signals, as an important physiological signal, reflect the state of the heart. Monitoring ECG signals can help detect certain heart diseases (such as angina and coronary heart disease) for prevention or treatment. Alternatively, monitoring ECG signals can guide fitness or exercise training by monitoring the body's movement. Monitoring devices typically use electrodes to acquire physiological signals. For example, heart rate monitors acquire ECG signals through electrodes that contact the skin. Summary of the Invention

[0003] This specification provides one or more embodiments of a flexible conductive patch configured to be attached between an electrode and biological tissue to transmit electrical signals from the biological tissue to the electrode.

[0004] In some embodiments, the flexible conductive patch includes a hydrogel body and a sheet-like fabric; the sheet-like fabric is located within the hydrogel body.

[0005] In some embodiments, the yarn diameter of the sheet fabric ranges from 0.05 mm to 1 mm, and the fabric density ranges from 10 yarns / cm to 200 yarns / cm.

[0006] In some embodiments, the components of the hydrogel body include: hydrogel molecules, crosslinking agents, water-retaining agents, and conductive ions.

[0007] In some embodiments, the hydrogel body includes a first portion located on a first side of the sheet fabric and a second portion located on a second side of the sheet fabric, the first portion and the second portion having different viscosities.

[0008] In some embodiments, the hydrogel body includes a first portion located on a first side of the sheet fabric and a second portion located on a second side of the sheet fabric, wherein the first portion and the second portion have different components, and / or the components of the first portion and the components of the second portion have different component ratios.

[0009] In some embodiments, the thickness of the flexible conductive patch ranges from 0.05 mm to 5 mm.

[0010] In some embodiments, the thickness of the flexible conductive patch ranges from 0.1 mm to 0.5 mm.

[0011] In some embodiments, the surface area of ​​the flexible conductive patch is configured to be larger than the surface area of ​​the electrode.

[0012] In some embodiments, the resistance at both ends of the flexible conductive patch ranges from 1Ω to 100Ω.

[0013] One or more embodiments of this specification also provide a wearable device, comprising: at least two electrodes configured to acquire electrical signals from biological tissue; a wearable structure configured to carry the at least two electrodes; the at least two electrodes being spaced apart on the wearable structure; and at least one flexible conductive patch as described in some embodiments of this specification, the flexible conductive patch being configured to be detachably attached to the at least one electrode to transmit the electrical signals from the biological tissue to the electrode.

[0014] In some embodiments, the number of flexible conductive patches is less than the number of electrodes; the flexible conductive patches are configured to selectively attach to electrodes at different locations on the wearable structure.

[0015] In some embodiments, the number of flexible conductive patches is 2.

[0016] In some embodiments, the number of electrodes is an even number greater than 2; when the wearable structure is worn by a human body, an equal number of electrodes are distributed on both sides of the sagittal plane of the human body.

[0017] In some embodiments, the wearable structure is provided with at least two grooves corresponding to the at least two electrodes, and the electrodes are disposed in the corresponding grooves.

[0018] One or more embodiments of this specification also provide a method for manufacturing a flexible conductive patch, comprising: mixing hydrogel components to obtain a mixed liquid; the hydrogel components comprising: hydrogel molecules, a crosslinking agent, a water-retaining agent, and an electrolyte; curing the mixed liquid into a first sheet structure; laying a sheet fabric on the first sheet structure; pouring the mixed liquid onto the sheet fabric and curing it to obtain a second sheet structure having a sheet fabric interlayer; and cutting the second sheet structure to obtain the flexible conductive patch.

[0019] In some embodiments, mixing the hydrogel components to obtain a mixed liquid further includes: mixing a first hydrogel component to obtain a first mixed liquid; mixing a second hydrogel component to obtain a second mixed liquid; wherein the first hydrogel component is different from the second hydrogel component, and / or the component ratio of the first hydrogel component is different from the component ratio of the second hydrogel component; solidifying the mixed liquid into a first sheet structure further includes: solidifying the first mixed liquid into a first sheet structure; pouring the mixed liquid onto the sheet fabric and solidifying it to obtain a second sheet structure with a sheet fabric interlayer further includes: pouring the second mixed liquid onto the sheet fabric and solidifying it to obtain a second sheet structure with a sheet fabric interlayer.

[0020] In some embodiments, the proportion of hydrogel molecules in the first hydrogel component is different from the proportion of hydrogel molecules in the second hydrogel component.

[0021] One or more embodiments of this specification also provide a storage box for accommodating the flexible conductive patch described in some embodiments of this specification.

[0022] In some embodiments, the storage box is also used to hold a replenishment solution to immerse the flexible conductive patch in the replenishment solution for hydration.

[0023] In some embodiments, the inner wall of the box is provided with water level markings. Attached Figure Description

[0024] This application will be further described by way of exemplary embodiments, which will be described in detail with reference to the accompanying drawings. These embodiments are not limiting; in these embodiments, the same reference numerals denote the same structures, wherein:

[0025] Figure 1 is a schematic diagram of physiological electrical signal acquisition;

[0026] Figure 2 is a schematic diagram of physiological electrical signal acquisition according to some embodiments of this specification;

[0027] Figure 3 is a schematic diagram of the structure of a flexible conductive patch according to some embodiments of this specification;

[0028] Figure 4 is a schematic diagram of a flexible conductive patch and some dimensions according to some embodiments of this specification;

[0029] Figure 5 is a waveform diagram of electrical signals according to some embodiments of this specification;

[0030] Figure 6 is a flowchart illustrating a method for fabricating a flexible conductive patch according to some embodiments of this specification.

[0031] Figure 7 is a structural schematic diagram of a wearable device according to some embodiments of this specification;

[0032] Figure 8 is a structural schematic diagram of a wearable device according to some other embodiments of this specification;

[0033] Figure 9 is a schematic diagram of the human body;

[0034] Figure 10 is a schematic diagram of a wearable device usage scenario according to some embodiments of this specification;

[0035] Figure 11 is a schematic diagram of a wearable device in a usage scenario according to some other embodiments of this specification;

[0036] Figure 12 is a schematic diagram of a wearable device in a usage scenario according to some embodiments of this specification;

[0037] Figure 13 is a structural schematic diagram of a wearable device according to some embodiments of this specification;

[0038] Figure 14 is a structural schematic diagram of a storage box according to some embodiments of this specification.

[0039] Labels in the diagram: 100 Electrode; 200 Biological tissue; 210 Skin; 300 Flexible conductive patch; 310 Hydrogel body; 311 First part of hydrogel body; 312 Second part of hydrogel body; 320 Sheet fabric; 400 Electrical signal; 500 Storage box; 600 Replenishment fluid; 700 Wearable device; 710 Electrode on wearable device; 711 First electrode; 712 Second electrode; 720 Wearable structure; 721 Velcro or fastener; 722 Groove; 901 Centerline. Detailed Implementation

[0040] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are merely some examples or embodiments of this application. For those skilled in the art, these drawings can be applied to other similar scenarios without creative effort. Unless obvious from the context or otherwise specified, the same reference numerals in the drawings represent the same structures or operations.

[0041] Unless the context clearly indicates otherwise, some technical feature terms used in this specification are not singular and may include plural. Generally speaking, the terms "comprising" and "including" only indicate that explicitly identified steps and elements are included, and these steps and elements do not constitute an exclusive list; the method or apparatus may also include other steps or elements.

[0042] Flowcharts are used in this specification to illustrate the operations performed by the system according to embodiments of this specification. It should be understood that the preceding or following operations are not necessarily performed in exact order. Instead, the steps can be processed in reverse order or simultaneously. Furthermore, other operations can be added to these processes, or one or more steps can be removed from them.

[0043] Physiological signals carry information about the physical or chemical changes resulting from the physiological activities of an organism. This information can be detected and recorded to reflect the internal state of the body. Examples of physiological signals include electrocardiogram (ECG) signals, electroencephalogram (EEG) signals, electromyogram (EMG) signals, blood pressure signals, blood oxygen saturation, blood glucose levels, and so on. Physiological signals can be measured non-invasively or invasively using various sensors and devices, and are often analyzed using digital processing techniques to more accurately understand the physiological processes they represent. Specifically, electrocardiogram (ECG), EEG, and EMG signals can be non-invasively acquired using surface electrodes.

[0044] Figure 1 illustrates a schematic diagram of physiological electrical signal acquisition. Electrodes 100 are attached to biological tissue 200 to acquire electrical signals 400 from the biological tissue. Electrodes 100 can be metal fabric electrodes, conductive silicon electrodes, hydrogel electrodes, metal electrodes, etc. Biological tissue 200 can be human skin, animal skin, etc., and electrical signals 400 can be electrocardiogram (ECG), electroencephalogram (EEG), electromyogram (EMG), etc., signals from the biological tissue.

[0045] In the acquisition scenario shown in Figure 1, electrode 100 and biological tissue 200 are in direct contact. When the contact surface between electrode 100 and biological tissue 200 is relatively dry, there will be a large impedance between them, leading to significant signal loss during the acquisition of physiological electrical signals and affecting the accuracy of subsequent signal processing and calculation. Taking the use of a heart rate monitor as an example, a heart rate monitor is a portable device used to monitor and record cardiac activity, widely used in fitness, sports training, and medical monitoring. A heart rate monitor typically includes a wearable structure and electrodes. The wearable structure allows the heart rate monitor to be worn on the human body, with the electrodes in close contact with the skin to acquire electrocardiogram (ECG) signals. To ensure reliable ECG signal acquisition, users need to warm up and sweat to moisten the electrodes, thereby reducing the contact impedance between the electrodes and the skin. However, in cold seasons or non-fitness training applications (such as when the monitored subject is too weak to exercise), this method of reducing the contact resistance between the electrodes and the skin through warming up and sweating is no longer applicable.

[0046] In view of this, some embodiments of this specification provide a flexible conductive patch configured to be attached between an electrode and biological tissue to transmit electrical signals from the biological tissue to the electrode. The flexible conductive patch can efficiently and conveniently reduce the contact impedance between the electrode and the biological tissue, improving the stability and accuracy of physiological electrical signal acquisition.

[0047] Figure 2 is a schematic diagram of physiological electrical signal acquisition according to some embodiments of this specification. As shown in Figure 2, a flexible conductive patch 300 (or simply patch) is added between the electrode 100 and the biological tissue 200, so that the flexible conductive patch 300 and the electrode 100 are sequentially superimposed on the biological tissue 200, and the electrical signal 400 is transmitted to the electrode 100 through the flexible conductive patch 300. The flexible conductive patch 300 is flexible and can fully adhere to the electrode 100 and the biological tissue 200, avoiding increased contact resistance due to gaps at the contact surface. The flexible conductive patch 300 has a certain strength to maintain a stable geometric shape, such as a sheet-like shape. In some embodiments, the flexible conductive patch 300 is adhesive and can be directly pasted between the electrode 100 and the biological tissue 200. Furthermore, the flexible conductive patch 300 has the strength to support its complete removal from the adhered object (such as the electrode 100 or the biological tissue 200), so that the flexible conductive patch 300 can be reused. The flexible conductive patch 300 can be made of flexible conductive materials such as conductive gel, or it may contain conductive ions. The conductivity of the flexible conductive patch 300 can more effectively reduce the contact impedance between the electrode 100 and the biological tissue 200. According to some embodiments of this specification, the flexible conductive patch can quickly and significantly reduce the contact impedance between the electrode and the biological tissue, thereby improving the efficiency of physiological electrical signal acquisition.

[0048] Figure 3 is a schematic diagram of the structure of a flexible conductive patch according to some embodiments of this specification. As shown in Figure 3, the flexible conductive patch 300 may include a hydrogel body 310 and a sheet-like fabric 320, with the sheet-like fabric 320 located within the hydrogel body 310. In some embodiments, the hydrogel body 310 may have the same or similar geometric shape as the sheet-like fabric 320, such as the hydrogel body 310 also having a sheet-like shape. A sheet-like geometric shape can be understood as the area of ​​the surface of the geometric shape in a plane being greater than the dimension of the geometric shape in a direction perpendicular to the aforementioned plane. Alternatively, it can be intuitively understood as the length and width of the bottom surface (such as the upper or lower bottom surface) of the hydrogel body 310 or the sheet-like fabric 320 being greater than its thickness (the dimension perpendicular to the bottom surface). In some embodiments, the bottom surfaces of the hydrogel body 310 and the sheet-like fabric have the same or similar shapes; for example, their bottom surfaces may be rectangular, circular, elliptical, triangular, polygonal, etc. In some embodiments, the sheet fabric 320 can be considered as an internal interlayer within the hydrogel body 310, dividing the hydrogel body 310 into a first portion located on a first side of the sheet fabric 320 (the upper side of the sheet fabric 320 as shown in FIG. 3) and a second portion located on a second side of the sheet fabric 320 (the lower side of the sheet fabric 320 as shown in FIG. 3). In some embodiments, the bottom surface area of ​​the sheet fabric 320 is the same as the bottom surface area of ​​the hydrogel body 310, or the bottom surface area of ​​the sheet fabric 320 is smaller than the bottom surface area of ​​the hydrogel body 310. In some embodiments, the distances from the sheet fabric 320 to the upper and lower bottom surfaces of the hydrogel body 310 in the flexible conductive patch are the same or approximately the same, i.e., the aforementioned first portion and second portion have the same or similar thickness. In other embodiments, the sheet fabric 320 in the flexible conductive patch is closer to the upper bottom surface of the hydrogel body 310 or closer to the lower bottom surface of the hydrogel body 310. In some embodiments, due to the hydrophilic properties of the hydrogel, the first and second parts of the hydrogel body 310 do not have obvious breaks, or in other words, when viewed from the side of the flexible conductive patch, the first part of the hydrogel body 310, the sheet fabric 320, and the second part of the hydrogel body appear as an integrally formed structure.

[0049] In some embodiments of this specification, the hydrogel body possesses conductive and water-retaining properties. The conductive property enables the flexible conductive patch to effectively transmit bioelectrical signals to the electrodes during use, while the water-retaining property allows the flexible conductive patch to remain wetted for extended periods, ensuring effective conductivity and extending its service life. The hydrogel body described in some embodiments of this specification can be a hydrogel with a specific geometric shape. A hydrogel is a hydrophilic three-dimensional network structure gel that can be formed from water-soluble or hydrophilic polymers through specific chemical or physical cross-linking. In some embodiments of this specification, the water-soluble or hydrophilic polymers can also be referred to as hydrogel molecules, polymer molecules, or monomers. In some embodiments, the components of the hydrogel body may include: hydrogel molecules and cross-linking agents, and may further include water-retaining agents and conductive ions.

[0050] Hydrogel molecules and cross-linking agents are the basic components of the hydrogel matrix. For example, hydrogel molecules may include, but are not limited to: gelatin, alginate, cellulose derivatives, polyacrylic acid (PAA), polyvinyl alcohol (PVA), polyethylene glycol (PEG), polyacrylamide (PAM), etc., and cross-linking agents may include, but are not limited to: polyethylene glycol diacrylate, methacrylated gelatin, methacrylamide hyaluronic acid, etc. The cross-linking agent is used to link multiple hydrogel molecules together to form a stable three-dimensional network. By adjusting the component ratio of hydrogel molecules and cross-linking agents, the physical properties of the hydrogel matrix, such as strength, viscosity, and water retention, can be controlled. The strength of the hydrogel matrix can maintain its stable geometry, such as maintaining a sheet-like morphology, and also make the hydrogel matrix less prone to breakage during use. The viscosity of the hydrogel matrix allows flexible conductive patches to effectively adhere and fix to electrodes and biological tissues, facilitating use.

[0051] When the proportion of hydrogel molecules in the hydrogel bulk is greater than that of the crosslinking agent, the viscosity of the hydrogel increases. In some embodiments, the viscosity of the hydrogel bulk allows the flexible conductive patch to simultaneously achieve the purpose of fixing electrodes to biological tissue and facilitating peeling from biological tissue and electrodes. To quantitatively describe the viscosity of the hydrogel bulk, the following experimental conditions can be set: the experimental substrate is nitrile rubber, the width of the hydrogel bulk sample (the dimension perpendicular to the peeling force direction) is 20 mm, and the peeling speed is 200 mm / min. Under the aforementioned experimental conditions, the 180° peel force (the force required to remove the hydrogel body from the substrate at an angle of 180° with the substrate) of the hydrogel body samples provided in some embodiments of this specification is 0.06N to 0.6N, or 0.07N to 0.5N, or 0.08N to 0.4N, or 0.09N to 0.3N, or 0.1N to 0.2N, etc. For example, under the aforementioned experimental conditions, the 180° peel force of the hydrogel body samples provided in some embodiments of this specification can be 0.075N, 0.078N, 0.08N, 0.082N, 0.085N, 0.087N, 0.09N, 0.1N, etc. In some embodiments, when the 180° peel force of the hydrogel body exceeds 0.6N, it means that the viscosity of the hydrogel body is relatively high, and it may be difficult to peel the flexible conductive patch off the electrode or biological tissue intact.

[0052] When the proportion of crosslinking agent in the hydrogel matrix is ​​larger than that of hydrogel molecules, the crosslinking density of the hydrogel matrix increases, resulting in greater strength. Furthermore, the increased crosslinking density enhances the water-locking capacity of the hydrogel matrix, improving its water retention performance. Sheet-like fabrics can support the hydrogel matrix, improving the rigidity or strength of the flexible conductive patch. In some embodiments, the stretchable range of the flexible conductive patch is 0%-20% (dimensional change during stretching / unstretched dimension), or 0%-15%, for example, 0%-12%, or 0%-10%. In some embodiments, the tensile strength of the flexible conductive patch is not less than 5 MPa; for example, the tensile strength is 5.5 MPa, 6 MPa, or 8 MPa. Tensile strength, also known as tensile resistance, refers to the maximum stress a material (such as a flexible conductive patch) can withstand during stretching.

[0053] Sheet fabrics can be sheet-like materials formed by weaving yarns. For example, the yarn materials include, but are not limited to, cotton, linen, silk, polyester fiber, polypropylene, nylon, etc. In some embodiments, the yarns can be woven using plain weave, twill weave, mesh weave, or other similar methods to form the sheet fabric. In some embodiments, by configuring the yarn diameter and fabric density of the sheet fabric, the sheet fabric can possess a certain strength or rigidity while maintaining a certain tensile effect. Fabric density refers to the number of yarns per unit length of fabric, and is commonly used to describe the tightness of the fabric; it can be divided into warp density and weft density. In some embodiments, the yarn diameter of the sheet fabric can be 0.05mm to 1mm; for example, the yarn diameter can be 0.06mm, 0.07mm, 0.08mm, 0.09mm, etc. In some embodiments, the fabric density of the sheet fabric can be from 10 threads / cm to 200 threads / cm. For example, the warp density of the sheet fabric can be 15 threads / cm, 30 threads / cm, 50 threads / cm, 80 threads / cm, 100 threads / cm, 120 threads / cm, 150 threads / cm, 180 threads / cm, 190 threads / cm, etc. The weft density of the sheet fabric can be the same as or different from the warp density.

[0054] Water-retaining agents can further increase the water retention capacity of the hydrogel. Exemplary water-retaining agents may include glycerol, superabsorbent polymers (SAP), polyvinyl alcohol (PVA), polyethylene glycol (PEG), alginate, agar, gelatin, keratin, nano-silica, carbon nanotubes, and silver nanoparticles. In some embodiments, the water-retaining agents in the hydrogel can be detected by gas chromatography.

[0055] The conductive ions in the hydrogel give it conductive properties. These conductive ions can be provided by sodium chloride, potassium chloride, etc. In some embodiments, the conductive ions in the hydrogel can be detected by ion chromatography. In some embodiments, the signal transmission efficiency can be improved by configuring the resistance of the flexible conductive patch. For example, the resistance of the flexible conductive patch can be adjusted by adjusting the concentration or component ratio of the conductive ions in the hydrogel. Taking Figure 3 as an example, the resistance of the flexible conductive patch can be the measured resistance between the two ends of the flexible conductive patch 300, for example, the resistance between the upper and lower surfaces of the flexible conductive patch 300. In some embodiments, the resistance value at both ends of the flexible conductive patch is in the range of 1Ω to 100Ω. Specifically, the resistance value at both ends of the flexible conductive patch is in the range of 1Ω to 10Ω, or 10Ω to 50Ω, or 50Ω to 100Ω. For example, the resistance value at both ends of the flexible conductive patch can be 5Ω, 8Ω, 25Ω, 35Ω, 55Ω, 60Ω, 70Ω, 80Ω, or 90Ω, etc.

[0056] In some embodiments, the hydrogel body may also include other components to improve its physical or chemical properties. For example, the hydrogel body may also include antibacterial components, enabling the flexible conductive patch to exert antibacterial, anti-inflammatory, moisturizing, and repairing effects on biological tissues during use. Exemplary antibacterial components may include, but are not limited to, silver ions, hyaluronic acid, and tea tree oil. In other embodiments, the components of the hydrogel body may not contain cross-linking agents, in which case the hydrogel molecules can be cross-linked through physical processes.

[0057] Figure 4 illustrates a flexible conductive patch according to some other embodiments of this specification. As shown in Figure 4, the hydrogel body 310 of the flexible conductive patch includes a first portion 311 located on a first side (as above) of the sheet fabric 320 and a second portion 312 located on a second side (as below) of the sheet fabric 320. In some embodiments, the first portion 311 and the second portion 312 may have different physical properties; specifically, the first portion 311 and the second portion 312 may have different viscosities. In some embodiments, the viscosity of the portion of the hydrogel body in contact with biological tissue, such as user skin, may be lower to reduce the foreign body sensation during user use; the viscosity of the portion of the hydrogel body in contact with the electrode may be higher to increase fixation stability. In some embodiments, the first portion 311 and the second portion 312 may be made of materials with different components to achieve different physical properties between them, or a portion (such as the first portion 311 or the second portion 312) may be post-processed to change its physical properties so that they are different from the physical properties of the other portion (such as the second portion 312 or the first portion 311).

[0058] Continuing with the viscosity test conditions as an example: the experimental substrate is nitrile rubber, the width of the hydrogel sample (the dimension perpendicular to the peel force direction) is 20 mm, and the peel speed is 200 mm / min. The first part 311 of the hydrogel sample is attached to the experimental substrate, with a corresponding 180° peel force of 0.08 N. The second part 312 of the hydrogel sample is attached to the experimental substrate, with a corresponding 180° peel force of 0.06 N. Alternatively, the first part 311 of the hydrogel sample can be attached to the experimental substrate with a corresponding 180° peel force of 0.09 N, and the second part 312 with a corresponding 180° peel force of 0.07 N. Another example is attaching the first part 311 of the hydrogel sample to the experimental substrate with a corresponding 180° peel force of 0.15 N, and the second part 312 with a corresponding 180° peel force of 0.08 N.

[0059] In some embodiments, the first portion 311 and the second portion 312 of the hydrogel body shown in FIG. 4 may have different components and / or different component ratios. Taking the first portion 311 as the part of the hydrogel body in contact with the electrode and the second portion 312 as the part of the hydrogel body in contact with biological tissue as an example, the components of the first portion 311 may include hydrogel molecules, crosslinking agents, water-retaining agents, and conductive ions, while the components of the second portion 312 may include hydrogel molecules, crosslinking agents, water-retaining agents, conductive ions, and antibacterial components. Adding antibacterial components to the components of the hydrogel body in contact with biological tissue can improve the safety of the flexible conductive patch and protect biological tissue. In other embodiments, the component ratio of hydrogel molecules to crosslinking agents in the first portion 311 is higher, while the component ratio of hydrogel molecules to crosslinking agents in the second portion 312 is lower, thereby making the viscosity of the first portion 311 greater than that of the second portion 312.

[0060] Figure 4 also shows partial dimensions of the flexible conductive patch provided in some embodiments of this specification, where d represents the thickness and S represents the bottom surface area. In some embodiments, the thickness of the flexible conductive patch can affect the stability of bioelectrical signal transmission. Specifically, when the thickness of the flexible conductive patch is large, it is more prone to deformation, which can adversely affect the signal. Taking a heart rate monitor as an example, the electrodes of the heart rate monitor are attached to the user's skin through a flexible conductive patch. When the user exercises, such as running, a thicker flexible conductive patch is more prone to shear deformation (deformation of an object when subjected to an external force parallel to its surface). This deformation can easily affect the signal waveform and affect the stable transmission of the signal. Therefore, the thickness d of the flexible conductive patch provided in some embodiments of this specification can be set to 0.05mm to 5mm, further, it can be set to 0.08mm to 4mm, or 0.1mm to 3.5mm, or 0.1mm to 2mm, or 0.1mm to 1.5mm, or 0.1mm to 1mm, or 0.1mm to 0.5mm, or 0.5mm to 4mm, or 1mm to 3mm. As an example, the thickness d of the flexible conductive patch can be 0.2mm, 0.3mm, or 0.4mm, etc. The relatively small thickness of the flexible conductive patch provided in some embodiments of this specification can effectively prevent shear deformation and improve the stability of signal transmission.

[0061] The flexible conductive patch provided in some embodiments of this specification can improve the efficiency and stability of signal transmission. Figure 5 is an electrical signal waveform diagram according to some embodiments of this specification, wherein waveform 501 is the electrocardiogram waveform acquired without the flexible conductive patch between the human tissue and the electrode, and waveform 502 is the electrocardiogram waveform acquired with the flexible conductive patch added between the human tissue and the electrode. It can be seen that the electrocardiogram waveform (waveform 501) acquired without the flexible conductive patch between the human tissue and the electrode has a lot of noise interference, a low signal-to-noise ratio, and it is difficult to clearly identify the electrocardiogram wave characteristics; when the flexible conductive patch is used between the human tissue and the electrode, at least part of the noise in the acquired electrocardiogram waveform (waveform 502) is suppressed, the signal-to-noise ratio is improved, and the QRS complex, T wave, and other characteristics are more clearly displayed.

[0062] This specification also provides a method for manufacturing a flexible conductive patch in some embodiments, aiming to improve the production efficiency of flexible conductive patches. Figure 6 is a schematic flowchart of a method for manufacturing a flexible conductive patch according to some embodiments of this specification. As shown in Figure 6, the manufacturing method provided in some embodiments of this specification may include the following steps.

[0063] Step 610: Mix the hydrogel components to obtain a mixed liquid.

[0064] In some embodiments, the hydrogel component may include hydrogel molecules, crosslinking agents, water-retaining agents, and electrolytes. Detailed descriptions of the hydrogel molecules, crosslinking agents, and water-retaining agents can be found above and will not be repeated here. Electrolytes are compounds that can conduct electricity when dissolved in water or in a molten state. Exemplary electrolytes may include salts such as sodium chloride and potassium chloride. The electrolyte in the hydrogel component is used to provide conductive ions.

[0065] In some embodiments, a first hydrogel component and a second hydrogel component with different components and / or different component ratios can be prepared. Specifically, the first hydrogel component and the second hydrogel component are different. For example, the first hydrogel component includes hydrogel molecules, a crosslinking agent, a water-retaining agent, and an electrolyte, while the second hydrogel component includes hydrogel molecules, a crosslinking agent, a water-retaining agent, an electrolyte, and an antibacterial component. In other embodiments, the first hydrogel component and the second hydrogel component have the same component types, but the component ratios are different. For example, both the first and second hydrogel components include hydrogel molecules, a crosslinking agent, a water-retaining agent, and an electrolyte, but the component ratio of hydrogel molecules to crosslinking agents in the first hydrogel component (e.g., the ratio of the mass of hydrogel molecules to the mass of crosslinking agents) is different from the component ratio of hydrogel molecules to crosslinking agents in the second hydrogel component. For example, the proportion of hydrogel molecules in the first hydrogel component differs from that in the second hydrogel component. Specifically, the ratio of hydrogel molecules to crosslinking agent in the first hydrogel component is greater than that in the second hydrogel component, or the mass ratio of hydrogel molecules in the first hydrogel component relative to the total mass of the first hydrogel component is greater than that in the second hydrogel component relative to the total mass of the second hydrogel component. Further, the first hydrogel component is mixed to obtain a first mixed liquid, and the second hydrogel component is mixed to obtain a second mixed liquid.

[0066] Step 620: Solidify the mixed liquid into a first sheet-like structure.

[0067] In some embodiments, the mixed liquid can be poured into a mold, and the height of the mixed liquid in the mold can be set based on the desired thickness d of the flexible conductive patch. For example, the height of the mixed liquid can be d / 2, less than d / 2, or greater than d / 2. In some embodiments, a first mixed liquid can be poured into the mold first, or a second mixed liquid can be poured into the mold first.

[0068] Next, the liquid mixture in the mold is cured to obtain the first sheet-like structure. Specifically, the mold containing the liquid mixture can be transported to the curing station by a conveyor belt, where the liquid mixture in the mold can be cured and shaped by photocuring or thermocuring.

[0069] Step 630: Lay a sheet of fabric on the first sheet structure.

[0070] The sheet fabric is woven from yarn. In some embodiments, the woven sheet fabric can be pre-acquired and cut according to the cross-sectional profile of the mold so that the sheet fabric can fit the area of ​​the first sheet structure in the mold. Further explanation of the sheet fabric can be found above and will not be repeated here.

[0071] Step 640: Pour the mixed liquid onto the sheet fabric and solidify it to obtain the second sheet structure.

[0072] In some embodiments, the mold can be conveyed again to the liquid injection station via a conveyor belt to pour the liquid mixture onto the sheet fabric. The liquid mixture poured onto the sheet fabric can be the same as or different from the liquid mixture that forms the first sheet structure. For example, when the liquid mixture forming the first sheet structure is a first liquid mixture, the liquid mixture poured onto the sheet fabric can be a second liquid mixture, and vice versa.

[0073] In some embodiments, the height or thickness of the mixed liquid layer poured again into the mold can be set based on the thickness of the first sheet structure and the desired thickness d of the flexible conductive patch. As an example, the height of the mixed liquid can be d / 2, greater than d / 2, or less than d / 2.

[0074] Furthermore, the current mixed liquid in the mold is cured again to obtain a second sheet structure with sheet-like fabric interlayers. Specifically, the mold containing the mixed liquid can be transported back to the curing station via a conveyor belt, where the mixed liquid in the mold can be cured by photocuring or thermocuring. Due to the good hydrophilicity of hydrogels, after the mixed liquid is poured onto the mesh fabric, the three-dimensional mesh structure in the cured first sheet structure can combine with the hydrogel molecules and / or water molecules in the re-injected mixed liquid. When the re-injected mixed liquid is cured, no obvious discontinuities or interlayer boundaries are observed on the sides or longitudinal sections of the second sheet structure.

[0075] Step 650: Cut the second sheet structure to obtain a flexible conductive patch.

[0076] The solidified second sheet structure can be demolded and cut based on the electrode area or shape to obtain a flexible conductive patch. Specifically, the cut flexible conductive patch can be rectangular, circular, elliptical, triangular, polygonal, or other shapes. In some embodiments, the surface area of ​​the flexible conductive patch (also called the bottom area, as shown in Figure 4, bottom area S) can be the same size as the surface area of ​​the electrode to perfectly cover the electrode surface. Alternatively, the surface area of ​​the flexible conductive patch can be smaller than the surface area of ​​the electrode. Specifically, the ratio of the surface area of ​​the flexible conductive patch to the surface area of ​​the electrode is 0.5 to 1; for example, the aforementioned ratio can be 0.5, 0.6, 0.8, etc. In other embodiments, the surface area of ​​the flexible conductive patch can be larger than the surface area of ​​the electrode. A larger flexible conductive patch can transmit more electrical signals from biological tissue to the electrode, which can be considered as having a certain degree of amplification effect on the electrical signals. Further explanation regarding the relationship between the surface areas of the flexible conductive patch and the electrode can be found in the following description.

[0077] The flexible conductive patch manufacturing method provided in some embodiments of this specification can quickly and efficiently obtain flexible conductive patches with fabric interlayers, improving production efficiency. By adjusting the components or component ratios of the mixed liquid injected twice, flexible conductive patches with different physical or chemical properties on both sides can be obtained to meet different application requirements.

[0078] Some embodiments of this specification also provide a wearable device. Figures 7 and 8 are schematic diagrams of the structure of a wearable device according to some embodiments of this specification. As shown in Figure 7, the wearable device 700 includes at least two electrodes 710 (such as a first electrode 711, a second electrode 712, ...), a wearable structure 720, and a flexible conductive patch 300. The electrodes 710 are configured to collect electrical signals from biological tissues, the wearable structure 720 is configured to carry the electrodes 710, and the electrodes 710 can be spaced apart on the wearable structure 720. The flexible conductive patch 300 is configured to be detachably attached to at least one electrode 710 to transmit electrical signals from biological tissues to the electrode 710.

[0079] The wearable structure 720 can fix two or more electrodes 710 to the monitored object, such as in the waist area, head area, face area, back area, limbs, or chest area. The two or more electrodes 710 are spaced apart on the wearable structure 720. When the monitored object wears the wearable structure 720, the two or more electrodes 710 can be correspondingly fixed to different parts of the monitored object to collect electrical signals at different potentials. The potential difference formed between the different electrodes 710 can carry information about the physical or chemical changes caused by the physiological activities of the monitored object. In some embodiments, the wearable structure 720 can be an elastic band structure, and the electrodes 710 can be spaced apart on the band structure along a first extension direction (or length direction). The band structure can be fastened to the waist area, chest area, limbs, etc., of the monitored object by fastening the band structure or by using Velcro or buckles 721. In some embodiments, the wearable structure 720 can also be in the form of trousers or a skirt. Two or more electrodes 710 can be distributed at intervals along the circumference of the waistband of the trousers, and when a person wears the trousers, the electrodes 710 at the waistband can be fixed to the waist area of ​​the person. The first extending direction of the wearable structure 720 can be the length direction of the waistband or skirt after it is unfolded circumferentially.

[0080] In some embodiments, the electrode 710 can be a regular shape such as circular, elliptical, or rectangular, or other irregular shapes. The electrode 710 can be a metal fabric electrode, a conductive silicon electrode, a hydrogel electrode, a metal electrode, etc. In some embodiments, the dimension of the electrode 710 in the first extending direction or in the second extending direction (perpendicular to the first extending direction) should be as large as possible, provided that it does not exceed the dimension of the wearable structure 720 in the first extending direction or in the second extending direction, to ensure that the electrode 710 has a large electrical signal receiving area. As an example only, the surface area size of the electrode 710 can be 1cm×1cm, 1cm×2cm, 1cm×3cm, 1cm×4cm, 1cm×5cm, 2cm×2cm, 2cm×3cm, 2cm×4cm, 2cm×5cm, 3cm×3cm, 3cm×4cm, 3cm×5cm, 4cm×4cm, 4cm×5cm, or 5cm×5cm. In some embodiments, electrode 710 can be electrically connected to a signal processing circuit to transmit the acquired physiological electrical signals to subsequent circuits for processing and analysis. For example, electrode 710 can be connected to the processing circuit via a wire.

[0081] In some embodiments, the number of electrodes 710 may be 2, 3, 4, 5, etc. The multiple electrodes 710 on the wearable structure 720 may be arranged at equal or unequal intervals. For example, the distance between two adjacent electrodes on the wearable structure 720 may be 2cm, 3cm, 4cm, 5cm, 10cm, or 15cm, etc. In some embodiments, the number of flexible conductive patches 300 is less than the number of electrodes 710, and the flexible conductive patches 300 may be configured to be selectively attached to electrodes at different locations on the wearable structure. When the monitored object wears the wearable structure 720, the electrodes 710 with the flexible conductive patches attached are electrically connected to the corresponding parts of the monitored object, thereby receiving electrical signals from biological tissue. Optionally, the processing circuit in the wearable device may primarily read or only read and process the electrical signals collected by the electrodes 710 with the flexible conductive patches attached. For example, the flexible conductive patch 300 has a certain thickness. Electrodes 710 without the flexible conductive patch have little contact with the biological tissue of the monitored object, such as skin, and receive almost no electrical signals from the biological tissue. Alternatively, the surface area of ​​each electrode 710 can be set very small, for example, much smaller than the area of ​​the flexible conductive patch 300. Even if electrodes 710 without the flexible conductive patch are in contact with the biological tissue of the monitored object, such as skin, the electrical signals they collect are negligible. Further optionally, the signal transmission channel between the electrodes 710 without the flexible conductive patch and the processing circuit can be cut off. Therefore, by selectively attaching the flexible conductive patch 300 to electrodes at different locations on the wearable structure, the location for collecting biological tissue electrical signals can be flexibly adjusted, adapting to monitored objects of different body types and different measurement needs.

[0082] Figure 9 is a schematic diagram of the entire human body. Figure 9(a) shows the front view of the human body, and Figure 9(b) shows the back view. As shown in Figures 9(a) and (b), the sagittal plane of the human body refers to the plane that passes through the midline 901 and divides the human body into two equal or approximately equal parts. The midline 901 can be determined by a line connecting the tip of the nose to the midpoint between the nipples, a line connecting the midpoint between the nipples to the midpoint of the umbilicus, or a line connecting the midpoint of the umbilicus to the midpoint of the pubic symphysis joint. Positions A through F in Figure 9 are examples of different sites for collecting electrical signals from biological tissues in the human body. Positions A through F can be skin areas of a certain size; these positions can be inherent locations in the human anatomy, suitable for collecting specific physiological electrical signals (such as electrocardiogram signals). For example, positions A through F could be the fourth intercostal space at the left sternal border, the fifth intercostal space at the left midclavicular line, the left anterior superior iliac spine, the right anterior superior iliac spine, the left anterior and posterior iliac spines, and the lateral anterior and posterior iliac spines, respectively.

[0083] Figure 10 is a schematic diagram of the use scenario of a wearable device according to some embodiments of this specification. As shown in Figure 10, multiple electrodes 710 disposed on the wearable structure 720 can be concentrated along a certain section of the strip-shaped wearable structure 720 along the first extending direction. The spacing between adjacent electrodes can be set to be small, such as 1cm, 1.5cm, 2cm, etc. When a human wears the wearable structure 720, the multiple electrodes 710 are located at the skin 210. One side of two flexible conductive patches 300 can be attached to two of the multiple electrodes respectively. The other side of the aforementioned flexible conductive patches 300 can be attached to positions A and B of the human skin 210 respectively, thereby enabling the electrodes on the wearable device to accurately collect the electrical signals at positions A and B of the human body. For human bodies of different body types, the distance between positions A and B may be large or small. By flexibly selecting the electrodes to which the flexible conductive patches are attached, the wearable device can more compatiblely monitor the physiological electrical signals at positions A and B on different human bodies. Figure 11 is a schematic diagram of the use scenario of a wearable device according to some other embodiments of this specification. As shown in Figure 11, if it is necessary to obtain the potential difference between position A and position A' of the human body (position A' can be a position closer to position A than position B), the flexible conductive patch 300 originally attached to position B can be moved to position A', and the flexible conductive patch can be attached to another electrode 710 on the wearable structure 720 nearby, thereby conveniently obtaining the physiological electrical signals of positions A and A' of the human body.

[0084] In some embodiments, the number of electrodes 710 can be an even number greater than 2, and the number of flexible conductive patches is 2. Referring to Figure 8, an even number of electrodes 710 are spaced apart on the wearable structure 720. When the subject wears the wearable structure 720, an equal number of electrodes 710 can be distributed on both sides of the subject's midsagittal plane. In some embodiments, the wearable structure 720 can be worn on the waist of the human body. The electrodes 710 on the wearable structure 720 can be distributed at positions C to F. One side of each of the two flexible conductive patches can be attached to the electrodes near positions C and D, respectively, and the other side can be attached to positions C and D of the human body, thereby allowing the measurement of physiological electrical signals at positions C and D. For example, the flexible conductive patch originally attached to position C can be attached to the electrode near position E on the wearable structure 720, and the flexible conductive patch originally attached to position D can be attached to the electrode near position F on the wearable structure 720, thereby adjusting to measure the physiological electrical signals at positions E and F of the human body.

[0085] In some embodiments, the surface area of ​​the flexible conductive patch is greater than the surface area of ​​the electrode. Specifically, the surface area of ​​the flexible conductive patch can be no less than 1.2 times, 1.5 times, or 2 times the surface area of ​​the electrode, etc. Alternatively, the flexible conductive patch can have a larger dimension relative to the electrode in the first extension direction, such as the length of the flexible conductive patch in the first extension direction being no less than 1.1 times, 1.2 times, 1.3 times, 1.5 times, 2 times, or 2.5 times the length of the electrode in the first extension direction, etc. Setting the surface area of ​​the flexible conductive patch to be greater than the surface area of ​​the electrode can further improve the adaptability of the wearable device to different collection sites. Figure 12 is a schematic diagram of a usage scenario of the wearable device according to some embodiments of this specification. As shown in Figure 12, when a wearable structure 720 is worn on a human body and one electrode is aligned with a preset sampling point (such as position C), the other electrodes on the wearable structure 720 cannot be aligned with another preset sampling point (such as position D). Since the surface area of ​​the flexible conductive patch 300 is larger than the surface area of ​​the electrode 710, one side of the flexible conductive patch 300 can be attached to position D, and the other side can be attached to the nearest electrode at position D. Therefore, the wearable device can better accommodate different body shapes and acquire physiological electrical signals from preset sampling points.

[0086] In some embodiments, the wearable structure may have at least two grooves corresponding to at least two electrodes, with the electrodes disposed in the corresponding grooves. Figure 13 is a schematic structural diagram of a wearable device according to some embodiments of this specification. As shown in Figure 13, the wearable structure 720 has two or more grooves 722, the number of grooves 722 may be the same as the number of electrodes 710, and each groove 722 has a corresponding electrode 710 disposed therein. In some embodiments, the wearable structure is made of fabric, and holes may be formed in the wearable structure, with rigid groove structures disposed within the holes, and electrodes placed in the groove structures. For example, the grooves may be made of materials such as plastic or silicone. Another example is that the wearable structure may be an integrally molded silicone strip with grooves, with electrodes placed in the corresponding grooves. Yet another example is that the wearable structure may be an integrally woven structure, with groove structures woven into the electrode positions on the wearable structure, and electrodes placed therein. In some embodiments, the surface area of ​​the flexible conductive patch 300, or the surface area of ​​the side configured to attach to the electrode (the first portion 311 shown in FIG. 3), can be adapted to the opening area of ​​the groove 722. At least a portion of the flexible conductive patch 300 can be placed in the groove 722 and attached to the electrode 710 therein. The groove 722 on the wearable structure 720 can, on the one hand, enhance the stability of the attachment between the flexible conductive patch and the electrode, and on the other hand, further increase the distance between the electrode without the flexible conductive patch attached and the biological tissue, reducing interference.

[0087] It should be understood that the flexible conductive patch provided in some embodiments of this specification is not only suitable for use with wearable devices provided in conjunction with some embodiments of this specification, but can also be used in conjunction with any other electrodes for collecting physiological electrical signals.

[0088] The following uses a heart rate monitor as an example to further describe the application scenarios of the flexible conductive patch provided in some embodiments of this specification. In some embodiments, the wearable device is a heart rate monitor, which can be worn around the chest area or the waist area of ​​the human body. After wearing the heart rate monitor, the user can attach the flexible conductive patch between the ECG signal acquisition site and the electrodes of the heart rate monitor. The flexible conductive patch has a certain degree of adhesion, which can fix the electrodes at the acquisition site. The flexible conductive patch can effectively reduce the impedance between the human body acquisition site and the electrodes, improving the stability and accuracy of physiological electrical signal acquisition. Due to the certain strength of the flexible conductive patch, it is not easy for the user to fold it during use, avoiding different parts of the flexible conductive patch from sticking together due to folding. On the other hand, the strength and appropriate adhesion of the flexible conductive patch itself allow the user to easily peel the flexible conductive patch off the electrodes and skin after using the heart rate monitor, without easily tearing or damaging the flexible conductive patch. The flexible conductive patch provided in some embodiments of this specification has good water retention and can be used effectively for a long time. For example, the user can use the same flexible conductive patch when using the heart rate monitor multiple times. In some embodiments, the lifespan of a reusable flexible conductive patch can be extended by adding water.

[0089] Some embodiments of this specification also provide a storage box for storing flexible conductive patches, which can be placed in the storage box when the flexible conductive patches are not in use. Figure 14 is a structural schematic diagram of the storage box according to some embodiments of this specification. In some embodiments, the cross-section of the storage box 500 shown in Figure 14 in the horizontal direction can be various shapes such as rectangular, circular, elliptical, and polygonal. The storage box 500 may be equipped with a lid to slow down the water loss rate of the flexible conductive patch 300 placed in the storage box 500, and at the same time facilitate user carrying. In some embodiments, the storage box 500 may also be configured to hold a replenishment liquid 600. When the flexible conductive patch 300 is placed in the replenishment liquid 600, the hydrophilic properties of the hydrogel body allow the flexible conductive patch to automatically replenish water after being immersed in the replenishment liquid. In some embodiments, the replenishment liquid can be clean water. In some embodiments, a water level mark may be provided on the inner wall of the storage box. After the user places the flexible conductive patch in the box, they can refer to the water level mark to inject an appropriate amount of replenishment liquid to submerge the flexible conductive patch, thereby achieving the purpose of replenishment. The wettability of the flexible conductive patch is improved after water replenishment, and it still has good conductivity even after long-term and repeated use, ensuring the stability and accuracy of electrical signal transmission.

[0090] The beneficial effects of some embodiments in this specification include, but are not limited to, the following aspects: (1) The flexible conductive patch used between the electrode and biological tissue can effectively reduce the impedance between the motor and biological tissue and improve the signal transmission efficiency; (2) The hydrogel body of the flexible conductive patch has good water retention, does not require frequent water replenishment, and has a long service life; (3) The flexible conductive patch can be reused multiple times, reducing the cost of use; (4) The flexible conductive patch has a certain strength, which can prevent the patch from bending or sticking due to excessive softness during use, thus improving the ease of use; (5) The flexible conductive patch has a moderate viscosity, which ensures the fixation effect while making it easy to remove from the electrode and biological tissue, and at the same time reduces the foreign body sensation when the user uses it; (6) The flexible conductive patch can be used as an extension of the electrode in wearable devices, adapting to users of different body types and different measurement needs; (7) The manufacturing method of the flexible conductive patch can effectively improve production efficiency and efficiently prepare flexible conductive patches with different physical or chemical forms on both sides; (8) The flexible conductive patch can be used with a storage box to further improve its service life. It should be understood that the above-mentioned beneficial effects can be reflected in different embodiments of this specification, and the same embodiment may have more than one of the aforementioned beneficial effects at the same time.

[0091] The basic concepts have been described above. Obviously, for those skilled in the art, the detailed disclosure above is merely illustrative and does not constitute a limitation of this application. Although not explicitly stated herein, those skilled in the art may make various modifications, improvements, and corrections to this application. Such modifications, improvements, and corrections are suggested in this application, and therefore remain within the spirit and scope of the exemplary embodiments of this application.

[0092] Furthermore, this application uses specific terms to describe embodiments of the application. For example, "an embodiment," "one embodiment," and / or "some embodiments" refer to a particular feature, structure, or characteristic associated with at least one embodiment of the application. Therefore, it should be emphasized and noted that "an embodiment," "one embodiment," or "an alternative embodiment" mentioned twice or more in different locations in this specification do not necessarily refer to the same embodiment. In addition, certain features, structures, or characteristics in one or more embodiments of the application can be appropriately combined.

[0093] Similarly, it should be noted that, in order to simplify the description of the present application and thus aid in the understanding of one or more embodiments of the invention, the foregoing description of the embodiments of the present application sometimes combines multiple features into a single embodiment, drawing, or description thereof. However, this disclosure method does not imply that the subject matter of the application requires more features than those mentioned in the claims. In fact, the embodiments contain fewer features than all the features of the single embodiments disclosed above.

[0094] Finally, it should be understood that the embodiments described in this application are merely illustrative of the principles of the embodiments of this application. Other modifications may also fall within the scope of this application. Therefore, alternative configurations of the embodiments of this application are considered as examples and not limitations, and are regarded as consistent with the teachings of this application. Accordingly, the embodiments of this application are not limited to the embodiments explicitly described and illustrated in this application.

Claims

1. A flexible conductive patch, characterized in that, The flexible conductive patch is configured to be attached to an electrode and includes a hydrogel body and a sheet-like fabric; the sheet-like fabric is located within the hydrogel body. The tensile strength of the flexible conductive patch is not less than 5 MPa.

2. The flexible conductive patch according to claim 1, characterized in that, The 180° peel force of the hydrogel body is 0.06N to 0.6N.

3. The flexible conductive patch according to claim 1, characterized in that, The yarn diameter of the sheet fabric ranges from 0.05 mm to 1 mm, and the fabric density ranges from 10 yarns / cm to 200 yarns / cm.

4. The flexible conductive patch according to claim 1, characterized in that, The components of the hydrogel matrix include: hydrogel molecules, crosslinking agent, water-retaining agent, and conductive ions.

5. The flexible conductive patch according to claim 1, characterized in that, The hydrogel body includes a first portion located on a first side of the sheet fabric and a second portion located on a second side of the sheet fabric, the first portion and the second portion having different viscosities.

6. The flexible conductive patch according to claim 1, characterized in that, The hydrogel body includes a first portion located on a first side of the sheet fabric and a second portion located on a second side of the sheet fabric, wherein the first portion and the second portion have different components, and / or the components of the first portion and the components of the second portion have different component ratios.

7. The flexible conductive patch according to claim 1, characterized in that, The thickness of the flexible conductive patch ranges from 0.05 mm to 5 mm.

8. The flexible conductive patch according to claim 7, characterized in that, The thickness of the flexible conductive patch ranges from 0.1 mm to 0.5 mm.

9. The flexible conductive patch according to claim 1, characterized in that, The resistance range at both ends of the flexible conductive patch is 1Ω to 100Ω.

10. A wearable device, characterized in that, include: At least two electrodes are configured to acquire electrical signals from biological tissues; A wearable structure is configured to carry the at least two electrodes; The at least two electrodes are spaced apart on the wearable structure; In addition, at least one flexible conductive patch as described in any one of claims 1 to 9, the flexible conductive patch being configured to be detachably attached to at least one electrode to transmit the electrical signal from the biological tissue to the electrode.

11. The wearable device according to claim 10, characterized in that, The surface area of ​​the flexible conductive patch is configured to be larger than the surface area of ​​the electrode.

12. The wearable device according to claim 10, characterized in that, The number of flexible conductive patches is less than the number of electrodes; the flexible conductive patches are configured to selectively attach to electrodes at different locations on the wearable structure.

13. The wearable device according to claim 12, characterized in that, The number of flexible conductive patches is 2.

14. The wearable device according to claim 13, characterized in that, The number of electrodes is an even number greater than 2; when the wearable structure is worn by a human body, an equal number of electrodes are distributed on both sides of the sagittal plane of the human body.

15. The wearable device according to claim 10, characterized in that, The wearable structure is provided with at least two grooves corresponding to the at least two electrodes, and the electrodes are disposed in the corresponding grooves.

16. A method for manufacturing a flexible conductive patch, characterized in that, include: The hydrogel components are mixed to obtain a mixed liquid; The hydrogel components include: hydrogel molecules, crosslinking agents, water-retaining agents, and electrolytes; The mixed liquid is solidified into a first sheet-like structure; A sheet-like fabric is laid on the first sheet-like structure; The mixed liquid is poured onto the sheet fabric and solidified to form a second sheet structure with a sheet fabric interlayer. The second sheet structure is cut to obtain the flexible conductive patch.

17. The manufacturing method according to claim 16, characterized in that, The step of mixing the hydrogel components to obtain a mixed liquid further includes: mixing a first hydrogel component to obtain a first mixed liquid; and mixing a second hydrogel component to obtain a second mixed liquid; wherein the first hydrogel component is different from the second hydrogel component, and / or the component ratio of the first hydrogel component is different from the component ratio of the second hydrogel component; The step of solidifying the mixed liquid into a first sheet structure further includes: solidifying the first mixed liquid into a first sheet structure; The step of pouring the mixed liquid onto the sheet fabric and curing it to form a second sheet structure with a sheet fabric interlayer further includes: pouring the second mixed liquid onto the sheet fabric and curing it to form a second sheet structure with a sheet fabric interlayer.

18. The manufacturing method according to claim 17, characterized in that, The proportion of hydrogel molecules in the first hydrogel component is different from that in the second hydrogel component.

19. A storage box, characterized in that, For accommodating the flexible conductive patch as described in any one of claims 1 to 10.

20. The storage box according to claim 19, characterized in that, It is also used to hold replenishment fluid, so that the flexible conductive patch can be immersed in the replenishment fluid for water replenishment.

21. The storage box according to claim 19, characterized in that, The inner wall of the box is marked with a water level mark.

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