Skin-adhesive material-based perspiration hairpiece sensor, perspiration sensor

Abstract

The application discloses a kind of based on skin adhesive material's perspiration wig sensor, perspiration sensor.The skin adhesive material includes: hydrophobic adhesive layer, which includes the porous fiber network formed at least by pressure-sensitive adhesive and polyurethane, in the hole contained therein, the minimum distance between adjacent holes is defined as the hole spacing, the hole spacing is less than the minimum sweat gland pore diameter;Hydrophilic transport layer has the first hydrophilic fiber with material including first hydrophilic high molecular material and polyurethane;Super-hydrophilic diffusion layer has the second hydrophilic fiber with material including second hydrophilic high molecular material and polyurethane.By setting the hole spacing of the hole contained in the hydrophobic adhesive layer to be less than the minimum sweat gland pore diameter, to ensure that perspiration channel is unobstructed, avoid skin / device interface sweat accumulation, so that perspiration wig sensor, perspiration sensor has good adhesive stability and detection accuracy.

Description

Technical Field

[0001] This invention belongs to the field of flexible wearable physiological health monitoring sensor technology, specifically relating to a sweat-permeable wig sensor and a sweat-permeable sensor based on skin adhesion materials. Background Technology

[0002] Flexible sensors and wearable electronic devices can continuously monitor human physiological (bioelectricity, respiration, heart rate, etc.) and biochemical (sweat, etc.) information in real time, and have important application value in medical diagnosis, active health, sports rehabilitation and other fields. Flexible wearable electronic devices need to adhere tightly to the skin surface and maintain a stable skin-device interface during operation in order to obtain high-quality physiological and biochemical information.

[0003] However, existing flexible wearable electronic devices typically adhere to the skin via strong adhesives or films (medical double-sided tape). This often blocks sweat pores, causing sweat to accumulate at the skin-device interface, reducing the adhesion of the adhesive or film and hindering stable device adhesion. Furthermore, because normal heat dissipation through perspiration is obstructed, the hypothalamus, as the thermoregulatory center, continuously monitors body temperature. When reduced perspiration in the adhered area leads to insufficient heat dissipation, the hypothalamus sends stronger signals to other sweat glands in nearby areas, triggering compensatory sweating. This compensatory sweating problem has several impacts on flexible wearable electronic devices. For example, sweat accumulation at the skin-device interface reduces interface adhesion stability and can even cause device detachment, leading to sweat artifacts such as electrical signal drift and instability. It can also alter the spatiotemporal distribution of sweat on the skin surface and the secretory characteristics of sweat glands, significantly affecting the accuracy of wearable sensors in detecting sweat information (sweating rate, concentration, etc.). Summary of the Invention

[0004] To solve all or part of the above-mentioned technical problems, the present invention provides the following technical solutions: A first aspect of the present invention provides a sweat-wicking wig sensor, comprising: wig; A skin-adhesive material bonded to a wig, the skin-adhesive material comprising a hydrophobic adhesive layer, a hydrophilic transport layer and a superhydrophilic diffusion layer arranged sequentially, the hydrophobic adhesive layer being used to adhere to the human body; The detection mechanism includes a sweat detection electrode and an electroencephalogram (EEG) detection electrode, wherein the detection mechanism is disposed in a hydrophobic adhesive layer in the skin adhesive material for the side that is in contact with the human body; The hydrophobic adhesion layer comprises a porous fiber network formed at least by pressure-sensitive adhesive and polyurethane. The minimum distance between the edges of adjacent pores in the porous fiber network is defined as the pore spacing, which is less than the minimum sweat gland pore diameter. The hydrophilic transport layer comprises a first hydrophilic fiber, which is made of a first hydrophilic polymer and polyurethane. The superhydrophilic diffusion layer comprises a second hydrophilic fiber, which is made of a second hydrophilic polymer and polyurethane. The mass percentage of the second hydrophilic polymer in the superhydrophilic diffusion layer is greater than the mass percentage of the first hydrophilic polymer in the hydrophilic transport layer.

[0005] The sweat-wicking wig sensor provided by this invention possesses excellent breathability and sweat-wicking properties, as well as high accuracy in detecting physiological signals. Specifically, this invention ensures unobstructed sweat venting channels by setting the pore spacing of the porous fiber network in the hydrophobic adhesive layer of the skin adhesion material to be smaller than the minimum sweat gland pore diameter (20 μm), effectively preventing sweat accumulation at the skin / device interface. Furthermore, by combining a gradient wetting structure with a hydrophilic transport layer and a superhydrophilic diffusion layer, a directional sweat transport path is formed from the hydrophobic adhesive layer to the superhydrophilic diffusion layer, resulting in excellent breathability and sweat-wicking properties. This avoids sweat accumulation and solves the problem of low detection accuracy caused by compensatory sweating in existing technologies. Additionally, the hydrophobic adhesive layer based on pressure-sensitive adhesive and polyurethane also exhibits excellent adhesion properties, maintaining stable adhesion even after sweating.

[0006] In the described sweat-permeable wig sensor, the sweat detection electrode can be used to detect changes in the electrical conductivity of the scalp interface under resting conditions or low-intensity exercise, thereby assessing changes in scalp hydration and / or sweating rate; the EEG detection electrode can be used to collect brainwave signals from the head. Integrating the sweat detection electrode and the EEG detection electrode into the skin-adhesive material creates a sweat-permeable detection electrode that simultaneously detects dual-mode signals, enabling the monitoring of physiological signals while ensuring comfortable wear.

[0007] In some embodiments, the hole spacing is less than 20 μm.

[0008] In some embodiments, the mass ratio of pressure-sensitive adhesive to polyurethane (PU) in the hydrophobic adhesion layer is 2:1 to 1:3.

[0009] In some embodiments, the mass ratio of the first hydrophilic polymer material to polyurethane in the hydrophilic transport layer is 1:1 to 1:5.

[0010] In some embodiments, the mass ratio of the second hydrophilic polymer material to polyurethane in the superhydrophilic diffusion layer is 1:1 to 9:1.

[0011] In some embodiments, the pressure-sensitive adhesive includes one or more of acrylate (PA), silicone, and rubber.

[0012] In some embodiments, the first hydrophilic polymer material and the second hydrophilic polymer material include one or a combination of polyacrylonitrile (PAN), polyvinyl alcohol, and nylon 66, and the first hydrophilic polymer material and the second hydrophilic polymer material may be the same or different. In some embodiments, polyacrylonitrile can be selected for both, and similar spinning solution systems can avoid interfacial delamination of the fiber membrane and achieve better interfacial bonding.

[0013] Skin adhesion materials made from the aforementioned pressure-sensitive adhesive, polyurethane, and the aforementioned first and second hydrophilic polymer materials not only have excellent adhesion but also good comfort and biocompatibility, which can reduce the risk of scalp inflammation.

[0014] In some embodiments, the diameter of the fibers contained in the hydrophobic adhesion layer is 2 μm to 20 μm.

[0015] In some embodiments, the porosity of the hydrophobic adhesion layer is 30% to 50%, and the average diameter of the pores is 2 μm to 25 μm.

[0016] In some embodiments, the diameter of the first hydrophilic fiber in the hydrophilic transport layer is on the micrometer scale, for example, 1 μm to 5 μm.

[0017] In some embodiments, the porosity of the hydrophilic transport layer is 30% to 60%, and the average diameter of the pores is about 1 μm to 10 μm.

[0018] The hydrophilic transport layer, with its coarser fiber diameter and larger pore structure, reduces liquid transport resistance, accelerates liquid transport, and more effectively restricts the flow polymerization of the hydrophobic adhesive layer colloid, thus improving the stability of the adhesive layer. If the fiber diameter of the hydrophilic transport layer is too fine (e.g., less than 500 nm), the adhesive layer will flow and polymerize along the fibers to some extent, potentially clogging the perspiration pores.

[0019] In some embodiments, the diameter of the second hydrophilic fiber in the superhydrophilic diffusion layer is 0.5 μm to 3 μm.

[0020] In some embodiments, the porosity of the superhydrophilic diffusion layer is 30% to 70%, and the average diameter of the pores is about 1 μm to 15 μm.

[0021] In some embodiments, the second hydrophilic fibers in the superhydrophilic diffusion layer are arranged in an in-plane orientation. This in-plane orientation allows sweat reaching the superhydrophilic diffusion layer to be rapidly expelled, achieving more efficient sweat transfer at the skin / device interface.

[0022] In some embodiments, the method for preparing the skin adhesion material includes: A first spinning solution containing a second hydrophilic polymer material and polyurethane is provided, and the first spinning solution is made into a superhydrophilic diffusion layer using an electrospinning process; A second spinning solution containing a first hydrophilic polymer material and polyurethane is provided, and electrospinning is performed on the superhydrophilic diffusion layer using the second spinning solution to form a hydrophilic transport layer. A third spinning solution containing pressure-sensitive adhesive and polyurethane is provided, and the third spinning solution is used to electrospin on the hydrophilic transport layer to form a hydrophobic adhesion layer; The electrospinning process conditions for the hydrophobic adhesion layer include: a positive spinning voltage range of 8 to 18 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.1 to 1.5 mL / h, a spinning time of 50 to 100 min, a spinning temperature of 25°C to 45°C, and a relative humidity of 30%RH to 60%RH, so that the pore spacing between adjacent pores in the porous fiber network of the formed hydrophobic adhesion layer is smaller than the minimum sweat gland pore diameter.

[0023] The electrospinning process conditions of the above-mentioned hydrophobic adhesion layer can make the pore spacing of the porous fiber network smaller than the minimum sweat gland pore diameter (20μm).

[0024] In some embodiments, the process conditions for preparing the superhydrophilic diffusion layer include: a positive spinning voltage range of 8 to 25 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.5 to 1.5 mL / h, a spinning time of 50 to 200 min, and a receiver rotation speed of 300 rpm to 3000 rpm.

[0025] In some embodiments, when preparing the superhydrophilic diffusion layer, the receiver rotation speed is adjusted to 1000 rpm to 3000 rpm to induce the fibers to form an in-plane orientation.

[0026] In some embodiments, the mass ratio of the second hydrophilic polymer material to polyurethane in the first spinning solution is 1:1 to 9:1.

[0027] In some embodiments, the concentration of the first spinning solution is 10 wt% to 16 wt%.

[0028] In some embodiments, the process conditions for forming the hydrophilic transport layer include: a positive spinning voltage range of 8 to 20 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.8 to 1.8 mL / h, and a spinning time of 50 to 150 min.

[0029] In some embodiments, the mass ratio of the first hydrophilic polymer material to polyurethane in the second spinning solution is 1:1 to 1:5.

[0030] In some embodiments, the concentration of the second spinning solution is 10 wt% to 16 wt%.

[0031] In some embodiments, the mass ratio of pressure-sensitive adhesive to polyurethane in the third spinning solution is 2:1 to 1:3.

[0032] In some embodiments, the concentration of the third spinning solution is 10 wt% to 22 wt%.

[0033] In some embodiments, the solvents used in the first spinning solution, the second spinning solution, and the third spinning solution may include one or more of N,N-dimethylformamide (DMF), dimethylacetamide (DMAc), and dimethyl sulfoxide (DMSO), but are not limited thereto.

[0034] In some embodiments, an encapsulating adhesive layer is also formed on the superhydrophilic diffusion layer of the skin adhesion material, through which the skin adhesion material is bonded to the wig. The material of the encapsulating adhesive layer may include acrylate pressure-sensitive adhesive and polyacrylonitrile. For example, it can be obtained by electrospinning directly on the superhydrophilic diffusion layer using a spinning solution containing acrylate pressure-sensitive adhesive and polyacrylonitrile. It has good hydrophilicity and adhesion, thereby enabling the skin adhesion material to be bonded to other structures.

[0035] In some embodiments, the sweat-wicking wig sensor further includes a signal transmission mechanism connected to the detection mechanism for receiving and transmitting signals from the detection mechanism.

[0036] In some embodiments, the sweat detection electrode is an interdigital electrode.

[0037] In some embodiments, the EEG detection electrodes include channel electrodes and reference electrodes.

[0038] In some embodiments, the sweat detection electrode and the electroencephalogram (EEG) detection electrode are made of flexible conductive material.

[0039] For example, the sweat detection electrode and the EEG detection electrode can be made of materials such as PEDOT:PSS, silver nanowires, carbon paste, Ag / AgCl, copper / gold electrodes, etc., and can be prepared by processes such as spraying, screen printing, and vapor deposition. The EEG detection electrode can also be made of hydrogel electrodes, fabric electrodes, microneedle electrodes, etc.

[0040] A second aspect of the present invention provides a perspiration sensor, comprising: A skin adhesion material comprising a hydrophobic adhesion layer, a hydrophilic transport layer and a superhydrophilic diffusion layer arranged sequentially, wherein the hydrophobic adhesion layer is used to adhere to the human body; A sweat collection chamber, wherein the sweat collection chamber is located within the surface of the skin-adhesive material; A microchannel, one end of which is connected to a sweat collection chamber; Sweat testing facilities are used to detect the concentration of electrolytes in sweat and the rate of sweating. The hydrophobic adhesion layer comprises a porous fiber network formed at least by pressure-sensitive adhesive and polyurethane. The minimum distance between the edges of adjacent pores in the porous fiber network is defined as the pore spacing, which is less than the minimum sweat gland pore diameter. The hydrophilic transport layer comprises a first hydrophilic fiber, which is made of a first hydrophilic polymer and polyurethane. The superhydrophilic diffusion layer comprises a second hydrophilic fiber, which is made of a second hydrophilic polymer and polyurethane. The mass percentage of the second hydrophilic polymer in the superhydrophilic diffusion layer is greater than the mass percentage of the first hydrophilic polymer in the hydrophilic transport layer.

[0041] The described sweat sensor exhibits excellent breathability and perspiration permeability, as well as high accuracy in detecting physiological signals. Specifically, by setting the pore spacing of the porous fiber network in the hydrophobic adhesion layer of the skin adhesion material to be smaller than the minimum sweat gland pore size (20 μm), unobstructed sweat channels are ensured, effectively preventing sweat accumulation at the skin / device interface. Combined with the gradient wetting structure of the hydrophilic transport layer and the superhydrophilic diffusion layer, a directional sweat transport path is formed from the hydrophobic adhesion layer to the superhydrophilic diffusion layer, resulting in excellent breathability and perspiration permeability. This avoids sweat accumulation and solves the problem of low detection accuracy caused by compensatory sweating in existing technologies. Furthermore, the hydrophobic adhesion layer based on pressure-sensitive adhesive and polyurethane also exhibits excellent adhesion properties, maintaining stable adhesion even after sweating.

[0042] In some embodiments, the sweat detection mechanism includes at least a first sweat detection electrode and a second sweat detection electrode, at least partially exposed within the microfluidic channel, allowing them to contact sweat flowing into the microfluidic channel for detection. The first and second sweat detection electrodes can be, for example, interdigital electrodes. The sweat detection electrodes can be made of materials such as PEDOT:PSS, silver nanowires, carbon paste, Ag / AgCl, or copper / gold electrodes, and can be prepared, for example, by processes such as spraying, screen printing, or vapor deposition. Electroencephalogram (EEG) detection electrodes can also be hydrogel electrodes, fabric electrodes, microneedle electrodes, etc.

[0043] In some embodiments, the perspiration sensor further includes a temperature detection mechanism for detecting skin temperature.

[0044] In some embodiments, the perspiration sensor further includes a signal transmission mechanism, which is at least used to collect and transmit the sweat signal detected by the sweat detection mechanism.

[0045] The skin adhesion materials in the sweat-permeable wig sensor described in the first aspect of the present invention and the sweat-permeable sweat sensor described in the second aspect are based on the same design concept. Therefore, further solutions for the skin adhesion materials in the sweat-permeable sweat sensor, such as the material selection, further structural features, and preparation methods of the hydrophobic adhesion layer, hydrophilic transport layer, and superhydrophilic diffusion layer, have been specifically described in the sweat-permeable wig sensor described in the first aspect, and therefore will not be repeated here.

[0046] Compared with the prior art, the present invention has at least some or all of the following beneficial effects: By setting the pore spacing (the minimum distance between the edges of adjacent pores) of the porous fiber network in the hydrophobic adhesive layer of the skin adhesive material to be less than the minimum sweat gland pore diameter (20 μm), the present invention ensures that the sweat pores have unobstructed perspiration channels, effectively preventing sweat accumulation. Based on this skin adhesive material, the perspiration-permeable wig sensor and perspiration sensor have good breathability and perspiration permeability, adhesion stability, and physiological signal detection accuracy, solving the problem of low detection accuracy caused by compensatory sweating in the prior art. Attached Figure Description

[0047] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0048] Figure 1 These are SEM images of the hydrophobic adhesion layers formed at different electrospinning times in Example 1; Figure 2 This is a statistical graph of the pore spacing in the hydrophobic adhesion layer formed by different electrospinning times in Example 1; Figure 3a This is a comparison diagram of the skin adhesion material of Example 1 and a commercial porous adhesive (purchased from 3M China Co., Ltd.); Figure 3b This is a schematic diagram of the hydrophobic adhesion layer design principle of the present invention; Figure 4 These are SEM images and physical images of the skin adhesion material prepared in Example 1 when the spinning time was 80 min; Figure 5 This is a comparison diagram of the water contact angles of the superhydrophilic diffusion layer, the hydrophilic transport layer, and the hydrophobic adhesion layer prepared in Example 1 when the spinning time is 80 min. Figure 6 This is a comparison chart of the physiological sweating rate of sweat glands and the sweat transfer rate of the skin adhesion material (spinning time of hydrophobic adhesion layer is 80 min) in Example 1. Figure 7 This is a comparison chart of the air permeability of the skin adhesion material of Example 1 (spinning time of hydrophobic adhesion layer is 80 min) and the adhesion adhesive of the prior art; Figure 8 This is a comparison chart of the adhesion strength of the skin adhesion material (spinning time of hydrophobic adhesion layer is 80 min) in Example 1 and existing adhesives before and after sweating. Figure 9 This is a comparison diagram of the peel strength of the hydrophobic adhesion layer formed by different electrospinning times in Example 1; Figure 10 The image shows a comparison of the peel strength of the skin adhesion material (spinning time of the hydrophobic adhesion layer is 80 min) of Example 1 and two commercial wig films after 1 h, 24 h and 48 h of adhesion to the human body. Figure 11 This is a comparison chart of the skin peel-off performance of the skin adhesion material (spinning time of hydrophobic adhesion layer is 80 min) in Example 1 and commercial wig adhesive film; Figure 12 The following is an illustration of the scalp condition after the skin adhesion material (hydrophobic adhesion layer spinning time of 80 min) and commercial wig adhesive sheet of Example 1 were adhered to the scalp and removed after 12 h; Figure 13 This is a comparison chart of the liquid transport rates of skin adhesive materials made from in-plane oriented fibers prepared in Example 1 and non-oriented fibers prepared in Example 2, under the condition that the hydrophobic adhesive layer spinning time is the same. Figure 14 This is a schematic diagram of the structure of the sweat-wicking wig sensor prepared in Example 5; Figure 15This is a SEM image of the hydrophobic adhesion layer with electrodes formed in Example 5; Figure 16 These are test graphs showing the sweating intensity of a human body wearing the sweat-wicking wig sensor of Example 5 under different activity conditions; Figure 17 This is a diagram showing changes in brain signals in a human wearing the sweat-wicking wig sensor of Example 5 under low-intensity exercise conditions; Figure 18 This is a schematic cross-sectional view of the perspiration sensor in Example 6; Figure 19 This is a top view of the perspiration sensor in Example 6; Figure 20 This is a schematic diagram of the detection principle of the perspiration sensor in Example 6; Figure 21 This is a graph showing the sweat rate detection of the perspiration sensor in Example 6 and the fully enclosed sweat sensor in the prior art. Figure 22 This is a graph showing the electrolyte concentration detection of the perspiration sensor in Example 6 and the fully enclosed perspiration sensor in the prior art; in, Figure 18 , Figure 19 In the diagram, each number represents: 11-sweat gland, 12-hypothionema, 13-skin epidermis, 2-hydrophobic adhesion layer, 3-hydrophilic transport layer, 4-superhydrophilic diffusion layer, 5-encapsulation adhesive layer, 6-sweat collection chamber, 7-detection mechanism, 8-sweat detection mechanism, 81-first sweat detection electrode, 82-second sweat detection electrode, 9-temperature detection mechanism, 10-microchannel. Detailed Implementation

[0049] The invention will be more fully understood through the following detailed description of its embodiments. The detailed embodiments disclosed herein are merely illustrative, and the invention may be embodied in various forms. Therefore, the specific functional details disclosed herein should not be construed as limiting, but rather as the basis for the claims.

[0050] In addition, unless otherwise specified, all raw materials used in the following embodiments can be purchased from the market or other sources, and all production and testing equipment used are known in the art, as are the testing methods used.

[0051] Example 1 Example 1 provides a skin adhesion material and its preparation method, specifically including the following steps: (1) Provide a first spinning solution with a concentration of 16 wt% and a PAN:PU mass ratio of 1:1. Set the positive spinning voltage range to 15 kV, the negative spinning voltage range to -2 kV, the spinning solution injection speed to 1.0 mL / h, the receiver rotation speed to 2500 rpm, and the spinning time to 80 min to obtain a superhydrophilic diffusion layer. (2) A hydrophilic transport layer is formed by direct electrospinning on the superhydrophilic diffusion layer, including: preparing a second spinning solution with a concentration of 16 wt% and a PAN:PU mass ratio of 1:4, setting the positive spinning voltage range to 15 kV and the negative spinning voltage range to -3 kV, the spinning solution injection speed to 1.0 mL / h, and the spinning time to 60 min, so as to form a hydrophilic transport layer; (3) Electrospinning a hydrophobic adhesion layer on the hydrophilic transport layer, and controlling the pore spacing between adjacent pores in the porous fiber network of the hydrophobic adhesion layer by adjusting the spinning time. Specific process conditions include: dissolving PU in N,N-dimethylformamide (DMF) to prepare a PU solution with a concentration of 22 wt%; mixing the PU solution with the PA solution to prepare a third spinning solution with a PA to PU mass ratio of 1:1; setting the positive spinning voltage range to 12 kV and the negative spinning voltage range to -1 kV; controlling the spinning solution injection rate to 0.2 mL / h; controlling the spinning time to be 10 min, 20 min, 40 min, 60 min, 80 min, 100 min, 120 min, and 150 min respectively; and controlling the spinning temperature to be 30℃ and the relative humidity to be 30%RH to form a hydrophobic adhesion layer.

[0052] Figure 1 This is a SEM image of the hydrophobic adhesion layer formed by different electrospinning times in Example 1. Figure 2 This is a statistical chart showing the pore spacing in the hydrophobic adhesion layer formed by different electrospinning times in Example 1. The pore spacing was measured by using ImageJ software to delineate and measure the pore spacing within a selected area of ​​the SEM image, and then statistically analyzing its distribution. Combined with... Figure 1 , Figure 2 It is known that the pore spacing gradually increases with increasing spinning time. Studies have found that when the spinning time is controlled within the range of 50-100 minutes, the porous fiber network of the hydrophobic adhesion layer can achieve a pore spacing of less than 20 μm between adjacent pores, resulting in good perspiration wicking and excellent adhesion properties. The optimal spinning time is 80 minutes, at which point the combined performance of perspiration wicking and adhesion is further improved. Figure 2 As shown, if the spinning time is less than 50 minutes, the fiber distribution of the adhesive layer is very loose, the adhesion performance is poor, and it cannot stably and firmly adhere to the skin; if the spinning time is greater than 100 minutes, the proportion of pores with a spacing greater than 20 μm increases, which can easily cause most sweat pores to be blocked, affecting the excretion of sweat.

[0053] Figure 3a This is a comparison chart of the skin adhesion material (spinning time of hydrophobic adhesion layer was 80 min) of Example 1 and a commercial porous adhesive (purchased from 3M China Co., Ltd.). Figure 3b This is a schematic diagram illustrating the design principle of the hydrophobic adhesion layer of this invention. The diameter of human sweat pores ranges from 20μm to 60μm, with a density of approximately 40-500 pores / cm². -2 .like Figure 3a Existing commercially available porous adhesives typically use methods such as laser cutting to create porous structures. The pore size and density of these adhesives do not match the actual sweat pores, leading to partial blockage of these pores. For example... Figure 3b As shown, this invention controls the electrospinning process conditions of the hydrophobic adhesion layer to increase the pore spacing (D) between adjacent pores in the porous fiber network of the hydrophobic adhesion layer. h The minimum distance between edges of adjacent pores is less than the minimum sweat gland pore diameter (D). g (i.e., 20μm), ensuring that the sweat pores are not completely covered by the fibers in the hydrophobic adhesion layer, allowing for smooth perspiration; while if D... h Greater than D g Sweat pores are easily blocked, leading to obstructed perspiration.

[0054] Figure 4 These are SEM images and physical images of the skin adhesion material prepared when the hydrophobic adhesion layer spinning time was 80 min in this embodiment. According to... Figure 4 It can be seen that the hydrophobic adhesion layer has a porous fiber network structure with a pore spacing of less than 20 μm between adjacent pores; the fibers in the superhydrophilic diffusion layer are arranged in an in-plane orientation.

[0055] Figure 5 This is a comparison diagram of the water contact angles of the superhydrophilic diffusion layer, the hydrophilic transport layer, and the hydrophobic adhesion layer prepared in this embodiment at a spinning time of 80 min, as shown in the figure. Figure 5 It can be seen that the water contact angles of the superhydrophilic diffusion layer, the hydrophilic transport layer, and the hydrophobic adhesion layer are 12.5°, 86.5°, and 124.4°, respectively, indicating that the superhydrophilic diffusion layer has superhydrophilicity, the hydrophilic transport layer has good hydrophilicity, and the hydrophobic adhesion layer has good hydrophobicity.

[0056] Figure 6 This is a comparison chart of the physiological sweating rate of sweat glands and the sweat transport rate of the skin adhesion material (spinning time of hydrophobic adhesion layer is 80 min) prepared in this embodiment. The physiological sweating rate of sweat glands is less than 3.33 μm / min. -1 cm -2The method for testing the sweat transfer rate of the skin adhesion material prepared in this embodiment is as follows: liquid is continuously output from the hydrophobic adhesion layer side at different rates through a simulated sweating platform, and the liquid is transferred from the hydrophobic adhesion layer side to the superhydrophilic diffusion layer side; until the liquid output rate of the simulated sweating platform reaches 2887 μm / min. -1 cm -2 The liquid cannot be completely transferred from the hydrophobic adhesion layer side to the superhydrophilic diffusion layer side. This rate is the sweat transport rate of the skin adhesion material prepared in this embodiment. After normalizing the above rate, the following is obtained: Figure 6 result.

[0057] Figure 7 This is a comparison chart of the air permeability of the skin adhesion material prepared in this embodiment (spinning time of the hydrophobic adhesion layer was 80 min) and the existing adhesives (purchased from 3M, Keep, Commas, Haishenuo, and commercial wig tape purchased from Walker Tape Co., Inc., USA). The test method was as follows: Following ASTM E96 standard, the test was conducted in a constant temperature and humidity chamber at 25°C and 30% relative humidity. The test procedure was as follows: 30 grams of deionized water were placed in a glass bottle with an opening diameter of 10 mm, the bottle opening was sealed with the sample to be tested, and the bottle was placed in the constant temperature chamber for 7 days. Mass loss (Δm) was recorded every 24 hours during this period. The result was calculated as follows: the water evaporation rate was calculated using the formula: Δm / (A×T), where A is the opening area of ​​the bottle and T is the total test time. Figure 7 The term "open" in the middle indicates that the bottle opening is not covered with any material and is in an open system. According to... Figure 7 It can be seen that the skin adhesive material prepared in this embodiment has breathability comparable to that of the open system, indicating that the skin adhesive material prepared in this embodiment has excellent breathability.

[0058] Figure 8 This is a comparison chart of the adhesion strength of the skin adhesion material (spinning time of hydrophobic adhesion layer is 80 min) prepared in this embodiment and existing adhesives (purchased from 3M, Haishenuo, Keep and Commas respectively) before and after sweating.

[0059] Figure 9 This is a comparison chart of the peel strength of the hydrophobic adhesion layer formed by different electrospinning times in this embodiment, combined with... Figure 9 , Figure 1 As shown, with the increase of spinning time of the hydrophobic adhesive layer, the effective adhesion area increases and the adhesion performance increases. Therefore, the measured peel strength increases with the increase of spinning time.

[0060] Figure 10This is a comparison of the peel strength of the skin adhesion material (spinning time of the hydrophobic adhesion layer was 80 min) and commercial wig adhesive (purchased from Walker Tape Co., Inc., USA) at 1 h, 24 h, and 48 h after adhesion to the human body. Figure 10 As shown, the adhesive strength of commercial wig film decreased by 64% after 48 hours of adhesion compared to the initial strength, while the skin adhesive material of Example 1 only decreased by 22% after 48 hours of adhesion, indicating that it has better adhesive stability.

[0061] Figure 11 This is a comparison of the skin-peeling performance of the skin adhesion material (spinning time of the hydrophobic adhesion layer was 80 min) in this embodiment and a commercial wig film (purchased from Walker Tape Co., Inc., USA). The electron microscope image on the right is an SEM image of the surface of the torn commercial wig film and the skin adhesion material of Example 1. Figure 11 As shown, the skin adhesion material of this embodiment has better skin conformal adhesion performance. Furthermore, the electron micrographs show that the surface of the commercial film is covered with stratum corneum, indicating that it causes more severe tearing damage to the stratum corneum. In contrast, the skin adhesion material of Example 1 has less stratum corneum on its surface after tearing, indicating that it causes less tearing damage to the stratum corneum.

[0062] Figure 12 The image shows the scalp after the skin adhesion material (hydrophobic adhesion layer spinning time was 80 min) and commercial wig adhesive (purchased from Walker Tape Co., Inc., USA) prepared in this embodiment were adhered to the scalp and removed after 48 hours, and compared with normal scalp (without any adhesive material). Figure 12 It is evident that the skin adhesion material of the present invention has a lower risk of skin inflammation and less sebum buildup in hair follicles, indicating that it has better biocompatibility.

[0063] Example 2 Example 2 is basically the same as Example 1, except that in step (1) of Example 2, the rotation speed of the receiver is 300 rpm; and in step (3), the spinning time of the hydrophobic adhesion layer is 80 min.

[0064] Because the receiver rotates at a lower speed in Example 2, the fibers in the resulting diffusion layer are unoriented. Figure 13 This is a comparison chart of the liquid transport rates of skin adhesion materials from Example 1 (in-plane oriented fibers) and Example 2 (non-oriented fibers) under the condition that the hydrophobic adhesion layer spinning time is the same. Figure 13 It can be seen that the in-plane orientation distribution of fibers can significantly improve the liquid transport rate.

[0065] Example 3 Example 3 provides a skin adhesion material and its preparation method, specifically including the following steps: (1) Provide a first spinning solution with a concentration of 10 wt% and a PAN:PU mass ratio of 9:1. Set the positive spinning voltage range to 8 kV, the negative spinning voltage range to -5 kV, the spinning solution injection speed to 0.5 mL / h, the receiver rotation speed to 1000 rpm, and the spinning time to 50 min to obtain a superhydrophilic diffusion layer. (2) A hydrophilic transport layer is formed by direct electrospinning on the superhydrophilic diffusion layer, including: preparing a second spinning solution with a concentration of 10 wt% and a PAN:PU mass ratio of 1:1, setting the positive spinning voltage range to 8 kV and the negative spinning voltage range to -5 kV, the spinning solution injection speed to 0.8 mL / h, and the spinning time to 50 min, so as to form a hydrophilic transport layer; (3) Electrospinning a hydrophobic adhesion layer on the hydrophilic transport layer, and controlling the pore spacing between adjacent pores in the porous fiber network of the hydrophobic adhesion layer by adjusting the spinning time. Specific process conditions include: dissolving PU in N,N-dimethylformamide (DMF) to prepare a PU solution with a concentration of 22 wt%; mixing the PU solution with the PA solution to prepare a third spinning solution with a PA:PU mass ratio of 2:1; setting the positive spinning voltage range to 8 kV, the negative spinning voltage range to -5 kV, the spinning solution injection rate to 0.1 mL / h, controlling the spinning time to 80 min, the spinning temperature to 25℃, and the relative humidity to 30%RH to form a hydrophobic adhesion layer.

[0066] Example 4 Example 4 provides a skin adhesion material and its preparation method, specifically including the following steps: (1) Provide a first spinning solution with a concentration of 16 wt% and a PAN:PU mass ratio of 6:1, set the positive spinning voltage range to 25 kV, the negative spinning voltage range to -0.5 kV, the spinning solution injection speed to 1.5 mL / h, the receiver rotation speed to 2500 rpm, and the spinning time to 200 min to obtain a superhydrophilic diffusion layer. (2) A hydrophilic transport layer is formed by direct electrospinning on the superhydrophilic diffusion layer, including: preparing a second spinning solution with a concentration of 16 wt% and a PAN:PU mass ratio of 1:5, setting the positive spinning voltage range to 20 kV and the negative spinning voltage range to -0.5 kV, the spinning solution injection speed to 1.8 mL / h, and the spinning time to 150 min, so as to form a hydrophilic transport layer; (3) Electrospinning a hydrophobic adhesion layer on the hydrophilic transport layer, and controlling the pore spacing between adjacent pores in the porous fiber network of the hydrophobic adhesion layer by adjusting the spinning time. Specific process conditions include: dissolving PU in N,N-dimethylformamide (DMF) to prepare a PU solution with a concentration of 22 wt%; mixing the PU solution with the PA solution to prepare a third spinning solution with a PA:PU mass ratio of 1:3; setting the positive spinning voltage range to 18 kV, the negative spinning voltage range to -0.5 kV, the spinning solution injection rate to 1.5 mL / h, controlling the spinning time to 80 min, the spinning temperature to 45℃, and the relative humidity to 60%RH to form a hydrophobic adhesion layer.

[0067] Example 5 Example 5 provides a sweat-permeable wig sensor based on the skin adhesion material of the present invention. Using the skin adhesion material from Example 1 (with an electrospinning time of 80 min for the hydrophobic adhesion layer), a sweat-permeable wig sensor is further prepared, including: (1) Place an electrode mask on the skin side of the hydrophobic adhesive layer of the skin adhesive material and spray 4 mL of 2.0wt% PEDOT:PSS solution to form interdigitated sweat detection electrodes on the hydrophobic adhesive layer. The width of the interdigitated electrodes is 100μm. (2) Preparation of EEG detection electrodes: Place an electrode mask in the area where the hydrophobic adhesion layer is attached to the skin, spray 6 mL of 2.0 wt% PEDOT:PSS solution to form EEG detection electrodes on the hydrophobic adhesion layer; In this embodiment, the EEG detection electrodes include 2 channel electrodes and 1 reference electrode.

[0068] (3) A hydrophilic encapsulating adhesive layer is prepared by electrospinning on the side of the superhydrophilic diffusion layer of the skin adhesive material away from the hydrophilic transport layer. The encapsulating adhesive layer has a sweat-permeable adhesive effect. The preparation process conditions include: preparing a spinning solution with a PA to PAN mass ratio of 1:1, setting the positive spinning voltage range to 13 kV and the negative spinning voltage range to -2 kV, and the spinning solution injection rate to 0.2 mL / h to obtain the encapsulating adhesive layer.

[0069] (4) Then, the side of the encapsulation adhesive layer away from the superhydrophilic diffusion layer is bonded to the inner edge of the wig; and the signal transmission mechanism (specifically the wireless transmission module in this embodiment) is fixed on the top of the wig, and the interface of the signal transmission mechanism is connected to the sweat detection electrode and the EEG detection electrode to realize real-time wireless data transmission.

[0070] Figure 14 This is a schematic diagram of the structure of the sweat-wicking wig sensor prepared in Example 5. Figure 15 This is a SEM image of the hydrophobic adhesion layer with electrodes formed in Example 5, as shown below. Figure 15As shown, the electrode is stably fixed on the fiber in a semi-embedded form on the hydrophobic adhesion layer to form a conductive network, but it will not block the sweat-permeable pores of the hydrophobic adhesion layer.

[0071] Figure 16 These are the sweating intensities measured by the human body wearing the aforementioned sweat-wicking wig sensor under different activity conditions. Figure 17 This is a diagram showing changes in brain signals in a person wearing the aforementioned sweat-wicking wig sensor under low-intensity exercise conditions.

[0072] Example 6 Example 6 provides a perspiration sensor based on the skin adhesion material of the present invention. Figure 18 , Figure 19 These are a cross-sectional view and a top view of the sweat sensor in this embodiment, combined with... Figure 18 , Figure 19 It can be seen that the sweat sensor includes: The skin adhesion material prepared in Example 1 (spinning time of the hydrophobic adhesion layer is 80 min) has its hydrophobic adhesion layer 2 adhering to the human skin epidermis 13. Figure 18 The paper also shows the sweat glands 11 and the hypodermis 12 present in the human skin sweating system. An encapsulation adhesive layer 5 is also formed on the side of the superhydrophilic diffusion layer 4 of the skin adhesion material away from the hydrophilic transport layer (the preparation method of the encapsulation adhesive layer 5 is the same as that in Example 5).

[0073] A sweat collection chamber 6, forming a ring-shaped closed area, is formed within the surface of the skin-adhesive material. The sweat collection chamber 6 extends from top to bottom through the encapsulation adhesive layer 5, the superhydrophilic diffusion layer 4, the hydrophilic transport layer 3, and the hydrophobic adhesive layer 2. In this embodiment, the sweat collection chamber 6 is formed by casting and curing patterned polydimethylsiloxane.

[0074] A detection mechanism 7 is attached to the encapsulation adhesive layer 5. A microchannel 10 is provided on the detection mechanism 7, and the inlet of the microchannel 10 communicates with the sweat collection chamber 6, allowing sweat to enter the sweat collection chamber through the microchannel 10. The detection mechanism 7 includes a sweat detection mechanism 8 and a temperature detection mechanism 9. The sweat detection mechanism 8 includes a first sweat detection electrode 81 and a second sweat detection electrode 82, at least partially exposed within the microchannel 10, allowing contact with sweat flowing into the microchannel 10 for detection. The temperature detection mechanism 9 is used to detect skin temperature. In this embodiment, both the first sweat detection electrode 81 and the second sweat detection electrode 82 are interdigitated electrodes with internal copper metal and gold-plated surfaces.

[0075] The perspiration sensor also includes a signal transmission mechanism (specifically a wireless transmission module in this embodiment), which is located on the top of the detection mechanism 7 and is used to collect and transmit the signals detected by the detection mechanism 7.

[0076] Figure 20 This is a schematic diagram of the detection principle of the perspiration sensor in this embodiment, where ΔG is... Figure 20 The vertical axis represents the change in conductivity at each step, and the horizontal axis represents the change in time corresponding to each step. ΔG / ΔT represents the differential of the conductivity change. Since the conductivity value changes with sweat concentration, a concentration change curve can be obtained. The time change at each step is related to the amount of sweat flowing through; therefore, ΔT / ΔG can establish a relationship with the sweating rate. When sweat enters through the microchannel inlet and passes through the sweat detection electrode, it causes a change in the total resistance of the entire circuit. This is equivalent to an increase in the number of resistors in a parallel circuit, resulting in a decrease in the total resistance and an increase in the conductivity. As sweat passes through the sweat detection electrode, the conductivity signal undergoes a sudden change, forming a conductivity "step" signal. The height of the "step" is correlated with the change in sweat concentration, and the width of the "step" is correlated with the sweating rate. By analyzing these signals separately, dual-mode signal decoupling can be achieved.

[0077] Figure 21 This is a graph showing the sweat rate detection of the perspiration sensor in Example 6 and the fully enclosed sweat sensor in the prior art ("skin-mounted microfluidic systems for measuring secretory fluidic pressures generated at the surface of the skin by eccrine sweat glands"). Figure 22 This is a graph comparing the electrolyte concentration of the breathable sweat sensor in Example 6 with that of a fully enclosed sweat sensor in the prior art (from "Wearable sweat loss measuring devices: From the role of sweat loss to advanced mechanisms and designs"). The fully enclosed sweat sensor in the prior art blocks sweat pores in non-detection areas. To meet the body's normal sweating and heat dissipation mechanisms, the sweat pores in the detection area trigger a compensatory mechanism, resulting in abnormal sweating. This causes the sweat rate detected by the sweat sensor to not reflect the actual sweating situation. In contrast, the breathable sweat sensor in Example 6 does not block sweat pores in non-detection areas, does not affect normal sweating, and does not cause compensatory sweating in the detection area, thus obtaining more accurate sweating information.

[0078] In addition, the inventors of this case also conducted experiments with other raw materials, process operations, and process conditions described in this specification, referring to the aforementioned embodiments, and obtained relatively ideal results in all cases.

[0079] All aspects, embodiments, features, and examples of this invention should be considered illustrative and used to explain and illustrate the invention, but not to limit it. The scope of the invention is defined only by the claims.

[0080] Although the invention has been described with reference to the above embodiments, those skilled in the art will understand that various other changes, omissions, and / or additions can be made without departing from the spirit and scope of the invention, and that substantially equivalents can be substituted for elements in the described embodiments. Therefore, the invention is not intended to be limited to the specific embodiments disclosed, but rather to encompass all embodiments falling within the scope defined by the claims.

Claims

1. A sweat-wicking wig sensor based on a skin-adhesive material, characterized in that, include: wig; A skin-adhesive material bonded to a wig, the skin-adhesive material comprising a hydrophobic adhesive layer, a hydrophilic transport layer and a superhydrophilic diffusion layer arranged sequentially, the hydrophobic adhesive layer being used to adhere to the human body; The detection mechanism includes a sweat detection electrode and an electroencephalogram (EEG) detection electrode, wherein the detection mechanism is disposed in a hydrophobic adhesive layer in the skin adhesive material for the side that is in contact with the human body; The hydrophobic adhesion layer comprises a porous fiber network formed at least by pressure-sensitive adhesive and polyurethane. The minimum distance between the edges of adjacent pores in the porous fiber network is defined as the pore spacing, which is less than 20 μm. The hydrophilic transport layer comprises a first hydrophilic fiber, which is made of a first hydrophilic polymer and polyurethane. The superhydrophilic diffusion layer comprises a second hydrophilic fiber, which is made of a second hydrophilic polymer and polyurethane. The mass percentage of the second hydrophilic polymer in the superhydrophilic diffusion layer is greater than the mass percentage of the first hydrophilic polymer in the hydrophilic transport layer.

2. The sweat-wicking wig sensor according to claim 1, characterized in that, The mass ratio of pressure-sensitive adhesive to polyurethane in the hydrophobic adhesion layer is 2:1 to 1:

3.

3. The sweat-wicking wig sensor according to claim 1, characterized in that, The pressure-sensitive adhesive includes one or more of acrylates, silicone, and rubber.

4. The sweat-wicking wig sensor according to claim 1, characterized in that, The mass ratio of the first hydrophilic polymer material to polyurethane in the hydrophilic transport layer is 1:1 to 1:

5.

5. The sweat-wicking wig sensor according to claim 1, characterized in that, The mass ratio of the second hydrophilic polymer material to polyurethane in the superhydrophilic diffusion layer is 1:1 to 9:

1.

6. The sweat-wicking wig sensor according to claim 1, characterized in that, The first hydrophilic polymer material and the second hydrophilic polymer material include one or a combination of polyacrylonitrile, polyvinyl alcohol, and nylon 66, and the first hydrophilic polymer material and the second hydrophilic polymer material may be the same or different.

7. The sweat-wicking wig sensor according to claim 1, characterized in that, The second hydrophilic fibers in the superhydrophilic diffusion layer are arranged in an in-plane orientation.

8. The sweat-wicking wig sensor according to any one of claims 1-7, characterized in that, The method for preparing the skin adhesion material includes: A first spinning solution containing a second hydrophilic polymer material and polyurethane is provided, and the first spinning solution is made into a superhydrophilic diffusion layer using an electrospinning process; A second spinning solution containing a first hydrophilic polymer material and polyurethane is provided, and electrospinning is performed on the superhydrophilic diffusion layer using the second spinning solution to form a hydrophilic transport layer. A third spinning solution containing pressure-sensitive adhesive and polyurethane is provided, and the third spinning solution is used to electrospin on the hydrophilic transport layer to form a hydrophobic adhesion layer; The electrospinning process conditions for the hydrophobic adhesion layer include: a positive spinning voltage range of 8 to 18 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.1 to 1.5 mL / h, a spinning time of 50 to 100 min, a spinning temperature of 25°C to 45°C, and a relative humidity of 30%RH to 60%RH, so that the pore spacing between adjacent pores in the porous fiber network of the formed hydrophobic adhesion layer is smaller than the minimum sweat gland pore diameter.

9. The sweat-wicking wig sensor according to claim 8, characterized in that, The process conditions for preparing the superhydrophilic diffusion layer include: a positive spinning voltage range of 8 ~ 25 kV, a negative spinning voltage range of -5 ~ -0.5 kV, a spinning solution injection rate of 0.5 ~ 1.5 mL / h, a spinning time of 50 ~ 200 min, and a receiver rotation speed of 300 rpm to 3000 rpm.

10. The sweat-wicking wig sensor according to claim 9, characterized in that, In the preparation of the superhydrophilic diffusion layer, the receiver rotation speed was adjusted to 1000 rpm to 3000 rpm to induce the fibers to form an in-plane orientation.

11. The sweat-wicking wig sensor according to claim 8, characterized in that, The process conditions for forming the hydrophilic transport layer include: a positive spinning voltage range of 8 to 20 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.8 to 1.8 mL / h, and a spinning time of 50 to 150 min.

12. The sweat-wicking wig sensor according to claim 8, characterized in that, The mass ratio of the second hydrophilic polymer material to polyurethane in the first spinning solution is 1:1 to 9:1, and / or the mass ratio of the first hydrophilic polymer material to polyurethane in the second spinning solution is 1:1 to 1:5, and / or the mass ratio of pressure-sensitive adhesive to polyurethane in the third spinning solution is 2:1 to 1:

3.

13. The sweat-wicking wig sensor according to claim 1, characterized in that, An encapsulating adhesive layer is also formed on the superhydrophilic diffusion layer of the skin adhesion material, through which the skin adhesion material is bonded to the wig.

14. The sweat-wicking wig sensor according to claim 1, characterized in that, The sweat-wicking wig sensor also includes a signal transmission mechanism, which is connected to the detection mechanism and is used to receive and transmit signals from the detection mechanism.

15. The sweat-wicking wig sensor according to claim 1, characterized in that, The sweat detection electrode is an interdigital electrode; and / or, the EEG detection electrode includes a channel electrode and a reference electrode; and / or, the sweat detection electrode and the EEG detection electrode are made of flexible conductive material.

16. A perspiration sensor based on a skin-adhesive material, characterized in that, include: A skin adhesion material comprising a hydrophobic adhesion layer, a hydrophilic transport layer and a superhydrophilic diffusion layer arranged sequentially, wherein the hydrophobic adhesion layer is used to adhere to the human body; A sweat collection chamber, wherein the sweat collection chamber is located within the surface of the skin-adhesive material; A microchannel, one end of which is connected to a sweat collection chamber; Sweat testing facilities are used to detect the concentration of electrolytes in sweat and the rate of sweating. The hydrophobic adhesion layer comprises a porous fiber network formed at least by pressure-sensitive adhesive and polyurethane. The minimum distance between the edges of adjacent pores in the porous fiber network is defined as the pore spacing, which is less than 20 μm. The hydrophilic transport layer comprises a first hydrophilic fiber, which is made of a first hydrophilic polymer and polyurethane. The superhydrophilic diffusion layer comprises a second hydrophilic fiber, which is made of a second hydrophilic polymer and polyurethane. The mass percentage of the second hydrophilic polymer in the superhydrophilic diffusion layer is greater than the mass percentage of the first hydrophilic polymer in the hydrophilic transport layer.

17. The perspiration sensor according to claim 16, characterized in that, The mass ratio of pressure-sensitive adhesive to polyurethane in the hydrophobic adhesion layer is 2:1 to 1:

3.

18. The perspiration sensor according to claim 16, characterized in that, The pressure-sensitive adhesive includes one or more of acrylates, silicone, and rubber.

19. The perspiration sensor according to claim 16, characterized in that, The mass ratio of the first hydrophilic polymer material to polyurethane in the hydrophilic transport layer is 1:1 to 1:

5.

20. The perspiration sensor according to claim 16, characterized in that, The mass ratio of the second hydrophilic polymer material to polyurethane in the superhydrophilic diffusion layer is 1:1 to 9:

1.

21. The perspiration sensor according to claim 16, characterized in that, The first hydrophilic polymer material and the second hydrophilic polymer material include one or a combination of polyacrylonitrile, polyvinyl alcohol, and nylon 66, and the first hydrophilic polymer material and the second hydrophilic polymer material may be the same or different.

22. The perspiration sensor according to claim 16, characterized in that, The second hydrophilic fibers in the superhydrophilic diffusion layer are arranged in an in-plane orientation.

23. The perspiration sensor according to any one of claims 16-22, characterized in that, The method for preparing the skin adhesion material includes: A first spinning solution containing a second hydrophilic polymer material and polyurethane is provided, and the first spinning solution is made into a superhydrophilic diffusion layer using an electrospinning process; A second spinning solution containing a first hydrophilic polymer material and polyurethane is provided, and electrospinning is performed on the superhydrophilic diffusion layer using the second spinning solution to form a hydrophilic transport layer. A third spinning solution containing pressure-sensitive adhesive and polyurethane is provided, and the third spinning solution is used to electrospin on the hydrophilic transport layer to form a hydrophobic adhesion layer; The electrospinning process conditions for the hydrophobic adhesion layer include: a positive spinning voltage range of 8 to 18 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.1 to 1.5 mL / h, a spinning time of 50 to 100 min, a spinning temperature of 25°C to 45°C, and a relative humidity of 30%RH to 60%RH, so that the pore spacing between adjacent pores in the porous fiber network of the formed hydrophobic adhesion layer is smaller than the minimum sweat gland pore diameter.

24. The perspiration sensor according to claim 23, characterized in that, The process conditions for preparing the superhydrophilic diffusion layer include: a positive spinning voltage range of 8 ~ 25 kV, a negative spinning voltage range of -5 ~ -0.5 kV, a spinning solution injection rate of 0.5 ~ 1.5 mL / h, a spinning time of 50 ~ 200 min, and a receiver rotation speed of 300 rpm to 3000 rpm.

25. The perspiration sensor according to claim 24, characterized in that, In the preparation of the superhydrophilic diffusion layer, the receiver rotation speed was adjusted to 1000 rpm to 3000 rpm to induce the fibers to form an in-plane orientation.

26. The perspiration sensor according to claim 23, characterized in that, The process conditions for forming the hydrophilic transport layer include: a positive spinning voltage range of 8 to 20 kV, a negative spinning voltage range of -5 to -0.5 kV, a spinning solution injection rate of 0.8 to 1.8 mL / h, and a spinning time of 50 to 150 min.

27. The perspiration sensor according to claim 23, characterized in that, The mass ratio of the second hydrophilic polymer material to polyurethane in the first spinning solution is 1:1 to 9:1, and / or the mass ratio of the first hydrophilic polymer material to polyurethane in the second spinning solution is 1:1 to 1:5, and / or the mass ratio of pressure-sensitive adhesive to polyurethane in the third spinning solution is 2:1 to 1:

3.

28. The perspiration sensor according to claim 23, characterized in that, The sweat detection mechanism includes at least a first sweat detection electrode and a second sweat detection electrode, at least partially exposed within the microchannel, enabling it to contact the sweat flowing into the microchannel for detection.

29. The perspiration sensor according to claim 23, characterized in that, It also includes a temperature detection device for detecting skin temperature.

30. The perspiration sensor according to claim 23, characterized in that, It also includes a signal transmission mechanism, at least for collecting and transmitting sweat signals detected by the sweat detection mechanism.

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