In-situ conductive bio-gel and method for preparing the same

Abstract

The application provides an in-situ conductive biological gel and a preparation method thereof. The in-situ conductive biological gel is prepared from the following raw materials: gelatin, a conductive polymer, a deep eutectic solvent and deionized water; and the mass ratio of the gelatin, the conductive polymer, the deep eutectic solvent and the deionized water is (1-100):1:(0.5-100):(1-300). The in-situ conductive biological gel provided by the application has high mechanical properties, strong adhesion, high conductivity and low signal-to-noise ratio. The preparation method of the in-situ conductive biological gel provided by the application is simple, the raw materials are cheap, the manufacturing process is pollution-free, and the in-situ conductive biological gel is conducive to large-scale production and has great industrial application potential.

Description

Technical Field

[0001] This invention relates to the field of medical conductive materials technology, specifically to an in-situ conductive biogel and its preparation method. Background Technology

[0002] Soft conductive materials play a crucial role in smart medical devices, energy applications, and brain-computer interfaces. In healthcare, typical applications of soft conductive materials involve the acquisition of electrophysiological signals, such as the detection of electrocardiograms (ECG) and electromyograms (EMG).

[0003] Common soft conductive materials include conductive elastomers, hydrogels, and organic hydrogels. However, current formulations of these conductive adhesive materials result in solid formation, often leading to a weak interface between the conductive material and the skin, insufficient bonding, and consequently a low signal-to-noise ratio (SNR).

[0004] Furthermore, conductive gels initially in a liquid state effectively address the insufficient adhesion issue present in solid gels. However, after gelation, these conductive gels typically face problems such as fragility, weak adhesion to the skin, and low signal-to-noise ratio. These factors significantly affect accurate and long-term detection, especially under conditions involving mechanical stress, such as motion detection via electromyography (EMG).

[0005] Therefore, there is an urgent need for an innovative formulation and method to create an in-situ gel liquid biogel with high mechanical properties, strong adhesion, high conductivity, and low signal-to-noise ratio. This biogel will be crucial for enhancing the detection of electrocardiogram (ECG) and electromyogram (EMG) signals. Summary of the Invention

[0006] To address the shortcomings of existing technologies, the present invention aims to provide an in-situ conductive biogel with high mechanical properties, strong adhesion, high conductivity, and low signal-to-noise ratio, which is crucial for enhancing the detection of electrocardiogram (ECG) and electromyogram (EMG) signals.

[0007] The first aspect of the present invention provides an in-situ conductive biogel, which is prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water; wherein the mass ratio of the gelatin, conductive polymer, deep eutectic solvent, and deionized water is (1-100):1:(0.5-100):(1-300).

[0008] In one embodiment of the present invention, the conductive polymer is at least one of PEDOT:PSS, PANI, and PPy.

[0009] In one embodiment of the present invention, the conductive polymer is PEDOT:PSS.

[0010] In one embodiment of the present invention, the deep eutectic solvent includes a hydrogen bond donor and a hydrogen bond acceptor, wherein the hydrogen bond donor is at least one selected from glycerol, urea, ethylene glycol, vanillic acid, sebacic acid, acetamide, phenol, benzamide, benzoic acid, malonic acid, thiourea, succinic acid, 1,3-dimethylurea, oxalic acid, lactic acid, citric acid, glucose, 1-methylurea, 1,1-dimethylurea, 1,4-butanediol, decanoic acid, fructose, triethylene glycol, dodecanoic acid, menthol, thymol, and 1-naphthol.

[0011] The hydrogen bond acceptor is at least one of choline chloride, lactic acid, choline carbonate, 2-(chlorocarbonyloxy)-N,N,N-trimethylethyleneamine chloride, benzyltriphenylphosphine chloride, lidocaine, proline, histidine, nicotinic acid, betaine, and tetramethylammonium chloride.

[0012] In one embodiment of the present invention, the deep eutectic solvent is composed of glycerol and choline chloride.

[0013] In one embodiment of the present invention, the mass ratio of the gelatin to the conductive polymer is (1-100):1.

[0014] In one embodiment of the present invention, the mass ratio of glycerin to gelatin is 1:(0.1-10).

[0015] In one embodiment of the present invention, the mass ratio of glycerol to choline chloride is 1:(0.1-10).

[0016] A second aspect of this invention provides a method for preparing the above-mentioned in-situ conductive biogel, comprising the following steps:

[0017] S1. Mix the hydrogen bond donor, the conductive polymer, and deionized water in the deep eutectic solvent to obtain the first mixture;

[0018] S2. Gelatin is introduced into the first mixture and dissolved and mixed at high temperature to obtain the second mixture;

[0019] S3. Add the hydrogen bond acceptor in the deep eutectic solvent to the second mixture, and place it in a high-temperature oven for 4-8 hours to eliminate residual bubbles, thus obtaining the third mixture.

[0020] S4. Place the obtained third mixture in an oven and dry it for 4-8 hours to remove moisture and obtain in-situ biogel.

[0021] In one embodiment of the present invention, step S1 specifically includes: mixing the hydrogen bond donor in the deep eutectic solvent with deionized water, and then adding the hydrogen bond donor in the deep eutectic solvent to mix, thereby obtaining a first mixture;

[0022] or,

[0023] Step S1 specifically includes: mixing the conductive polymer with deionized water, then adding a hydrogen bond donor from a deep eutectic solvent to obtain a first mixture.

[0024] Compared with the prior art, the embodiments of the present invention have the following beneficial effects:

[0025] 1. The in-situ conductive biogel provided in one embodiment of the present invention has high mechanical properties, strong adhesion, high conductivity and low signal-to-noise ratio, which is crucial for enhancing the detection of electrocardiogram (ECG) and electromyogram (EMG) signals.

[0026] 2. The in-situ conductive biogel provided in one embodiment of the present invention exhibits superior performance compared to existing commercial biogels in the detection of electrocardiogram (ECG) and electromyogram (EMG) signals. Clearly, the in-situ biogel provided by the present invention has enormous potential for industrial applications.

[0027] 3. In an embodiment of the present invention, the conductive polymer in the in-situ conductive biogel is PEDOT:PSS, the hydrogen bond donor is glycerol, and the hydrogen bond acceptor is choline chloride. PEDOT:PSS helps to improve electronic conductivity, while the combination of choline chloride and glycerol forms a deep eutectic solvent, thereby establishing ionic conductivity. Gelatin contributes to the in-situ gel properties and adhesion. In particular, the semi-interpenetrating network formed by PEDOT:PSS and gelatin enhances mechanical strength. These combined properties significantly improve the efficiency of electrocardiogram (ECG) and electromyography (EMG) detection.

[0028] 4. The in-situ conductive biogel preparation method provided in one embodiment of the present invention is simple, uses inexpensive raw materials, and is pollution-free in the manufacturing process, which is conducive to large-scale production and has great potential for industrial application. Attached Figure Description

[0029] To more clearly illustrate the technical solutions of the embodiments of the present invention, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are merely some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort. In the drawings:

[0030] Figure 1 The images show the state of the in-situ conductive biogel prepared in Example 1 immediately after being removed from the oven and one minute after removal.

[0031] Figure 2 The graph shows the mechanical property test results of the in-situ conductive biogel prepared in Example 1; wherein, Figure 2 A shows the tensile strength of in-situ biogels with different contents of deep eutectic solvent (0.37, 0.75, 1.12). Figure 2 B is the toughness diagram. Figure 2 C represents the tensile modulus diagram. Figure 2 D is the stress-strain curve. Figure 2 E is a diagram showing the pulling of a one-kilogram weight using the in-situ biogel from Example 1;

[0032] Figure 3 This is a graph showing the in-situ adhesion performance test results of the in-situ conductive biogel prepared in Example 1;

[0033] Figure 4 The image shows the adhesion test results between the in-situ conductive biogel prepared in Example 1 and the pigskin and electrodes; wherein, Figure 4 A shows the adhesion strength of in-situ biogels with different contents of deep eutectic solvent on pigskin. Figure 4 B is the adhesion strength diagram with the electrode. Figure 4 C represents the adhesion strength to pigskin in the presence of sodium chloride solution. Figure 4 D represents the adhesion strength between the electrode and the sodium chloride solution.

[0034] Figure 5 This is a data graph of electrocardiogram (ECG) signal testing using the in-situ conductive biogel provided in Example 1, wherein... Figure 5 A shows the electrode test diagrams for commercially available electrode sheets and the in-situ biogel prepared according to Example 1. Figure 5 B represents the measured signal-to-noise ratio prepared using commercial patches and the in-situ biogel provided in Example 1, as well as the signal-to-noise ratio graph after long-term application.

[0035] Figure 6 This is a data graph of electrocardiogram and electromyography (EMG) tests performed using the in-situ conductive biogel provided in Example 1, wherein... Figure 6 A shows the electromyographic signals of the arm prepared with the in-situ biogel provided in Example 1, compared with those of the commercial patch under repeated gripping conditions, as well as the electromyographic signal in the presence of sodium chloride solution. Figure 6 B is the corresponding myoelectric signal-to-noise ratio diagram. Detailed Implementation

[0036] The present invention will now be described in detail with reference to specific embodiments. These embodiments will help those skilled in the art to further understand the present invention, but do not limit the invention in any way. It should be noted that those skilled in the art can make several changes and improvements without departing from the concept of the present invention. These all fall within the protection scope of the present invention.

[0037] This invention proposes an in-situ conductive biogel, which is prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water.

[0038] To provide electronic conductivity, the conductive polymer PEDOT:PSS is added to the in-situ conductive biogel material system of the present invention to help improve electronic conductivity. Alternatively, the conductive polymer in the present invention can also be PANI or PPy.

[0039] To provide ionic conductivity, this invention introduces a deep eutectic solvent. The deep eutectic solvent comprises a hydrogen bond donor and a hydrogen bond acceptor. The hydrogen bond donor is at least one selected from glycerol, urea, ethylene glycol, vanillic acid, sebacic acid, acetamide, phenol, benzamide, benzoic acid, malonic acid, thiourea, succinic acid, 1,3-dimethylurea, oxalic acid, lactic acid, citric acid, glucose, 1-methylurea, 1,1-dimethylurea, 1,4-butanediol, decanoic acid, fructose, triethylene glycol, dodecanoic acid, menthol, thymol, and 1-naphthol. The hydrogen bond acceptor is at least one selected from choline chloride, lactic acid, choline carbonate, 2-(chlorocarbonyloxy)-N,N,N-trimethylethyleneamine chloride, benzyltriphenylphosphine chloride, lidocaine, proline, histidine, nicotinic acid, betaine, and tetramethylammonium chloride.

[0040] In one embodiment, glycerol acts as a hydrogen bond donor, and choline chloride acts as a hydrogen bond acceptor. In another embodiment, the hydrogen bond donor may be urea, and the hydrogen bond acceptor may be fluorinated choline. In another embodiment, the hydrogen bond donor may be ethylene glycol, and the hydrogen bond acceptor may be lactic acid. In yet another embodiment, the hydrogen bond donor may be vanillic acid, and the hydrogen bond acceptor may be choline carbonate.

[0041] In one embodiment, the conductive polymer is PEDOT:PSS, the hydrogen bond donor is glycerol, and the hydrogen bond acceptor is choline chloride. PEDOT:PSS contributes to improved electronic conductivity, while the combination of choline chloride and glycerol forms a deep eutectic solvent, thereby establishing ionic conductivity. Gelatin contributes to in-situ gelation properties and adhesion. In particular, the semi-interpenetrating network formed by PEDOT:PSS and gelatin enhances mechanical strength; these combined properties significantly improve the efficiency of electrocardiogram (ECG) and electromyography (EMG) detection.

[0042] The in-situ conductive biogel provided by this invention is liquid at temperatures exceeding 40°C.

[0043] This invention provides an in-situ conductive biogel. In this invention, "in-situ" means that in actual use, the liquid is usually applied to the skin, and the liquid gel will undergo a gelation process to adhere to the skin in the form of a soft biogel.

[0044] In one embodiment, the weight ratio of gelatin to PEDOT:PSS disclosed herein is 100:1. In another embodiment, the weight ratio of gelatin to PEDOT:PSS is 50:1. In yet another embodiment, the weight ratio of gelatin to PEDOT:PSS is 25:1. In yet another embodiment, the weight ratio of gelatin to PEDOT is from 1:1 to 100:1.

[0045] In one embodiment, the weight ratio of glycerol to water disclosed herein is 1:3. In another embodiment, the weight ratio of glycerol to water is 1:2. In another example, the weight ratio of glycerol to water is 1:1. In yet another embodiment, the weight ratio of glycerol to water is 1:0.5. In yet another example, the weight ratio of glycerol to water is 1:5. In yet another embodiment, the weight ratio of glycerol to water is from 1:0 to 1:10.

[0046] In one embodiment, the molar ratio of glycerol to choline chloride disclosed herein is 1:1. In another embodiment, the molar ratio of glycerol to choline chloride is 1:2. In another embodiment, the molar ratio of glycerol to choline chloride is 1:0.5. In yet another embodiment, the molar ratio of glycerol to choline chloride is 1:0.25.

[0047] In one embodiment, the weight ratio of glycerin to gelatin disclosed herein is 1:4. In another embodiment, the weight ratio of glycerin to gelatin is 1:2. In another example, the weight ratio of glycerin to gelatin is 1:1. In yet another embodiment, the weight ratio of glycerin to gelatin is 1:0.5. In yet another embodiment, the weight ratio of glycerin to gelatin is 1:5.

[0048] In this invention, "high temperature" refers to a temperature exceeding the liquid-solid transition temperature. Typically, the temperature exceeds 40°C, but it can also be a temperature exceeding 37°C.

[0049] The present invention will be further described below with reference to specific embodiments:

[0050] Example 1

[0051] This embodiment provides an in-situ conductive biogel, prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water. In this embodiment, the mass ratio of gelatin, conductive polymer, deep eutectic solvent, and deionized water is 2:0.02:1.75:3.

[0052] In this embodiment, the conductive polymer is PEDOT:PSS, which was purchased from Sigma.

[0053] In this embodiment, the deep eutectic solvent includes a hydrogen bond donor and a hydrogen bond acceptor, wherein the hydrogen bond donor is glycerol and the hydrogen bond acceptor is choline chloride.

[0054] In this embodiment, the gelatin and glycerin were purchased from Sigma, and the choline chloride was purchased from Macklin Inc.

[0055] The preparation method of the in-situ conductive biogel in this embodiment includes the following steps:

[0056] S1. Mix glycerol and deionized water evenly, then mix with PEDOT:PSS to obtain the first mixture;

[0057] S2. Gelatin is introduced into the first mixture and dissolved and mixed at high temperature to obtain the second mixture;

[0058] S3. Add choline chloride to the second mixture and put it into a sealed bottle. Let it stand in a high-temperature oven for 8 hours to eliminate residual bubbles and obtain the third mixture.

[0059] S4. Place the obtained third mixture into an oven, open the sealed bottle cap, and dry for 4 hours to remove moisture, thus obtaining an in-situ conductive biogel.

[0060] Figure 1 The images show the state of the in-situ conductive biogel prepared in this embodiment immediately after being removed from the oven and one minute after removal. Figure 1 As shown, when the in-situ conductive biogel obtained in this embodiment is transferred from the oven to the environment, the in-situ conductive biogel will solidify rapidly within 1 minute.

[0061] Example 2

[0062] This embodiment provides an in-situ conductive biogel, prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water. In this embodiment, the mass ratio of gelatin, conductive polymer, deep eutectic solvent, and deionized water is 2:0.02:0.87:3.5.

[0063] In this embodiment, the conductive polymer is PEDOT:PSS, which was purchased from Sigma.

[0064] In this embodiment, the deep eutectic solvent includes a hydrogen bond donor and a hydrogen bond acceptor, wherein the hydrogen bond donor is glycerol and the hydrogen bond acceptor is choline chloride.

[0065] In this embodiment, the gelatin and glycerin were purchased from Sigma, and the choline chloride was purchased from Macklin Inc.

[0066] The preparation method of the in-situ conductive biogel in this embodiment includes the following steps:

[0067] S1. Mix glycerol and deionized water evenly, then mix with PEDOT:PSS to obtain the first mixture;

[0068] S2. Gelatin is introduced into the first mixture and dissolved and mixed at high temperature to obtain the second mixture;

[0069] S3. Add choline chloride to the second mixture and put it into a sealed bottle. Let it stand in a high-temperature oven for 8 hours to eliminate residual bubbles and obtain the third mixture.

[0070] S4. Place the obtained third mixture into an oven, open the sealed bottle cap, and dry for 4 hours to remove moisture, thus obtaining an in-situ conductive biogel.

[0071] Example 3

[0072] This embodiment provides an in-situ conductive biogel, prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water. In this embodiment, the mass ratio of gelatin, conductive polymer, deep eutectic solvent, and deionized water is 2:0.02:2.62:2.5.

[0073] In this embodiment, the conductive polymer is PEDOT:PSS, which was purchased from Sigma.

[0074] In this embodiment, the deep eutectic solvent includes a hydrogen bond donor and a hydrogen bond acceptor, wherein the hydrogen bond donor is glycerol and the hydrogen bond acceptor is choline chloride.

[0075] In this embodiment, the gelatin and glycerin were purchased from Sigma, and the choline chloride was purchased from Macklin Inc.

[0076] The preparation method of the in-situ conductive biogel in this embodiment includes the following steps:

[0077] S1. Mix glycerol and deionized water evenly, then mix with PEDOT:PSS to obtain the first mixture;

[0078] S2. Gelatin is introduced into the first mixture and dissolved and mixed at high temperature to obtain the second mixture;

[0079] S3. Add choline chloride to the second mixture and put it into a sealed bottle. Let it stand in a high-temperature oven for 8 hours to eliminate residual bubbles and obtain the third mixture.

[0080] S4. Place the obtained third mixture into an oven, open the sealed bottle cap, and dry for 4 hours to remove moisture, thus obtaining an in-situ conductive biogel.

[0081] Example 4

[0082] This embodiment provides an in-situ conductive biogel, which is prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water.

[0083] In this embodiment, the conductive polymer is PEDOT:PSS, which was purchased from Sigma.

[0084] In this embodiment, the deep eutectic solvent includes a hydrogen bond donor and a hydrogen bond acceptor, wherein the hydrogen bond donor is glycerol and the hydrogen bond acceptor is choline chloride.

[0085] In this embodiment, the mass ratio of glycerol to water is 1:3.

[0086] In this embodiment, the mass ratio of glycerin to gelatin is 1:2.

[0087] In this embodiment, the mass ratio of gelatin to PEDOT:PSS is 10:1.

[0088] In this embodiment, the molar ratio of glycerol to choline chloride is 1:1.

[0089] In this embodiment, the gelatin and glycerin were purchased from Sigma, and the choline chloride was purchased from Macklin Inc.

[0090] The preparation method of the in-situ conductive biogel in this embodiment includes the following steps:

[0091] S1. Mix glycerol and deionized water evenly, then mix with PEDOT:PSS to obtain the first mixture;

[0092] S2. Gelatin is introduced into the first mixture and dissolved and mixed at high temperature to obtain the second mixture;

[0093] S3. Add choline chloride to the second mixture and put it into a sealed bottle. Let it stand in a high-temperature oven for 8 hours to eliminate residual bubbles and obtain the third mixture.

[0094] S4. Place the obtained third mixture into an oven, open the sealed bottle cap, and dry for 4 hours to remove moisture, thus obtaining an in-situ conductive biogel.

[0095] Comparative Example 1

[0096] The commercial conductive hydrogel provided in this comparative example is a commercial biogel called Jinnot ECG conductive gel, with a utilization ratio of 0.75.

[0097] Experimental Example

[0098] In this experimental example, the performance of the in-situ conductive biogels obtained in Examples 1-3 and the commercial conductive hydrogels provided in Comparative Example 1 were tested.

[0099] It should be noted that, Figure 2 A, Figure 2 B. Figure 2 C Figure 2 D、 Figure 4 A, Figure 4 B. Figure 4 C、、 Figure 4 In D, In-situ 0.37DE gela / P:P refers to the in-situ conductive biogel prepared in Example 2, In-situ 0.75DE gela / P:P refers to the in-situ conductive biogel prepared in Example 1, and In-situ 1.12DE gela / P:P refers to the in-situ conductive biogel prepared in Example 3. Figure 4 A, Figure 4 B. Figure 4 C Figure 4 D、 Figure 6 In A and 6B, the commercial biogel refers to the in-situ gel in Comparative Example 1. Figure 5 In A, the commercial biogel electrode refers to the commercial biogel electrode prepared from the biogel in the comparative example. Figure 5 In B, the in-situ gel electrode refers to the in-situ gel electrode prepared from the in-situ conductive biogel obtained in Example 1.

[0100] Mechanical property testing is conducted as follows: The prepared biogel is clamped onto the two end clamps of a mechanical testing machine and stretched axially to obtain the mechanical property results of the biogel. Figure 2 The graph shows the mechanical property test results of the biogel; among them, Figure 2 A shows the tensile strength diagrams of in-situ conductive biogels (Examples 1, 2, and 3) with different contents of deep eutectic solvent (0.37, 0.75, 1.12). Figure 2 B is a toughness diagram of the in-situ conductive biogel (Examples 1, 2, and 3). Figure 2 C is the tensile modulus diagram of the in-situ conductive biogel (Examples 1, 2, and 3). Figure 2 D is the stress-strain curve of the in-situ conductive biogel (Examples 1, 2, and 3). Figure 2 E is a diagram showing the pulling of a one-kilogram weight using the in-situ biogel from Example 1; by Figure 2 As can be seen from A, the biogels prepared in Examples 1, 2, and 3 all exhibit high tensile strength; Figure 2 As can be seen from B, the biogels prepared in Examples 1, 2, and 3 all exhibit good toughness; Figure 2 As can be seen from C, the elastic modulus of the biogels prepared in Examples 1, 2, and 3 is all less than 1 MPa, which is close to the elastic modulus of skin; Figure 2 As can be seen from D, the biogels prepared in Examples 1, 2, and 3 all exhibit good strain properties; Figure 2As can be seen from Example E, the biogel prepared in Example 1 exhibits good tensile properties. As described above, the in-situ conductive biogels provided in Examples 1-3 possess high tensile strength, compared to the tensile strength of the conventional commercial conductive hydrogels provided in the comparative examples, which is less than 1 MPa. The biogels provided in Examples 1-3 also exhibit a skin-like modulus (approximately <1 MPa), allowing deformation in accordance with skin deformation.

[0101] The in-situ adhesion performance test is conducted as follows: a gel material is coated between two pieces of pigskin (electrodes). After adhesion, a force is applied from both ends to stretch the material until the pigskin separates from the material. The required force is recorded to determine the adhesion strength. Figure 3 The in-situ adhesion performance test results of the biogel in Example 1 are shown in the figure. Due to the characteristics of in-situ gel, the surface of the gel prepared in Example 1 exhibits the same texture as the skin, highlighting the excellent interface between the biogel and the skin.

[0102] Figure 4 The figures shown are the adhesion test results between the bio-gel and pigskin and electrodes in Examples 1-3 and the comparative example. Figure 4 A shows the adhesion strength of in-situ biogels with different contents of deep eutectic solvent on pigskin. Figure 4 B is the adhesion strength diagram with the electrode. Figure 4 C represents the adhesion strength to pigskin in the presence of sodium chloride solution. Figure 4 D represents the adhesion strength diagram with the electrode in the presence of sodium chloride solution; from Figure 4 As can be seen from A, the biogels prepared in Examples 1-3 have adhesion strengths far exceeding those of commercial biogels, exceeding them by 35-140 times; Figure 4 As shown in B, the adhesion strength of the biogels prepared in Examples 1-3 to the electrodes is 20-150 times that of commercial biogels; Figure 4 As can be seen from C, the biogels prepared in Examples 1-3 still exhibit high adhesion strength to the skin even in sodium chloride solution; Figure 4 As shown in D, the biogels prepared in Examples 1-3 still exhibit high adhesion strength to the electrodes even in sodium chloride solution. In summary, the in-situ conductive biogels prepared in Examples 1-3 demonstrate superior adhesion strength to the skin and electrodes compared to commercial biogels (Comparative Example 1). The in-situ conductive biogels provided in Examples 1-3 demonstrate greater adhesion strength to the skin and electrodes than commercial biogels (Comparative Example 1).

[0103] Electrocardiogram (ECG) signal testing, the testing steps are as follows: Figure 5 As shown, the two electrodes are placed on the left and right wrists respectively, and the reference electrode is placed on the right ankle. When connected to an ECG device, the measurement can be obtained. Figure 5 This is a data graph showing the electrocardiogram (ECG) signal test performed using the in-situ conductive biogel provided in Example 1. Figure 5 A shows the electrode test diagrams for commercially available electrode sheets and the in-situ biogel prepared according to Example 1. Figure 5 B shows the measured signal-to-noise ratio (SNR) prepared using commercial patches and the in-situ biogel provided in Example 1, as well as the SNR graph after long-term application. (Refer to...) Figure 5 Electrocardiogram tests conducted by B showed that the in-situ conductive biogel provided in Example 1 exhibited a higher signal-to-noise ratio (SNR) than the commercial biogel (comparative example). Furthermore, even after 48 hours of use, the SNR of the in-situ conductive biogel remained high, surpassing the performance of the commercial gel after 24 hours of use.

[0104] Electromyography (EMG) signal testing is performed as follows: During the test, the patch is attached to the forearm, the patch is connected to the EMG device, and a signal is generated once by clenching the fist. Figure 6 In this context, "commercial patch panel" refers to... Figure 1 Single-use ECG electrodes; Figure 6 This is a data graph of electrocardiogram and electromyography (EMG) tests performed using the in-situ conductive biogel provided in Example 1, wherein... Figure 6 A shows the electromyographic signals of the arm prepared with the in-situ biogel provided in Example 1, compared with those of the commercial patch under repeated gripping conditions, as well as the electromyographic signal in the presence of sodium chloride solution. Figure 6 B is the corresponding myoelectric signal-to-noise ratio map. Figure 6 As can be seen, the in-situ conductive biogel provided in Example 1 exhibits superior signal quality and a higher signal-to-noise ratio (SNR) compared to commercial gels in electromyography (EMG) signal testing, even after immersion in NaCl solution simulating sweat conditions. This highlights its significant application potential in EMG testing.

[0105] Specific embodiments of the present invention have been described above. It should be understood that the present invention is not limited to the specific embodiments described above, and those skilled in the art can make various changes or modifications within the scope of the claims, which do not affect the essence of the present invention. Unless otherwise specified, the embodiments and features described in this application can be arbitrarily combined with each other.

Claims

1. An in-situ conductive biogel, characterized in that, It is prepared from the following raw materials: gelatin, conductive polymer, deep eutectic solvent, and deionized water; the mass ratio of the gelatin, conductive polymer, deep eutectic solvent, and deionized water is (1-100):1:(0.5-100):(1-300); The deep eutectic solvent includes hydrogen bond donors and hydrogen bond acceptors; The deep eutectic solvent is composed of glycerol and choline chloride; The conductive polymer is PEDOT:PSS; The mass ratio of glycerin to gelatin is 1:(0.1-10); The mass ratio of glycerol to choline chloride is 1:(0.1-10).

2. The method for preparing the in-situ conductive biogel according to claim 1, characterized in that, Includes the following steps: S1. Mix the hydrogen bond donor, the conductive polymer, and deionized water in the deep eutectic solvent to obtain the first mixture; S2. Gelatin is introduced into the first mixture and dissolved and mixed at high temperature to obtain the second mixture; S3. Add the hydrogen bond acceptor in the deep eutectic solvent to the second mixture, and place it in a high-temperature oven for 4 to 8 hours to eliminate residual bubbles, thereby obtaining the third mixture; S4. Place the obtained third mixture in an oven and dry it for 4 to 8 hours to remove moisture and obtain in-situ biogel.

3. The method for preparing the in-situ conductive biogel according to claim 2, characterized in that, Step S1 specifically includes: mixing the hydrogen bond donor in the deep eutectic solvent with deionized water, and then adding the hydrogen bond donor in the deep eutectic solvent to mix, to obtain a first mixture; or, Step S1 specifically includes: mixing the conductive polymer with deionized water, then adding a hydrogen bond donor from a deep eutectic solvent to obtain a first mixture.

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