CN113527605A - Tissue adhesion conductive porous hydrogel and preparation method thereof - Google Patents
Tissue adhesion conductive porous hydrogel and preparation method thereof Download PDFInfo
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- CN113527605A CN113527605A CN202110833840.6A CN202110833840A CN113527605A CN 113527605 A CN113527605 A CN 113527605A CN 202110833840 A CN202110833840 A CN 202110833840A CN 113527605 A CN113527605 A CN 113527605A
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08F—MACROMOLECULAR COMPOUNDS OBTAINED BY REACTIONS ONLY INVOLVING CARBON-TO-CARBON UNSATURATED BONDS
- C08F299/00—Macromolecular compounds obtained by interreacting polymers involving only carbon-to-carbon unsaturated bond reactions, in the absence of non-macromolecular monomers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
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- A—HUMAN NECESSITIES
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- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/52—Hydrogels or hydrocolloids
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08F—MACROMOLECULAR COMPOUNDS OBTAINED BY REACTIONS ONLY INVOLVING CARBON-TO-CARBON UNSATURATED BONDS
- C08F2/00—Processes of polymerisation
- C08F2/46—Polymerisation initiated by wave energy or particle radiation
- C08F2/48—Polymerisation initiated by wave energy or particle radiation by ultraviolet or visible light
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
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- C08K2201/001—Conductive additives
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K7/00—Use of ingredients characterised by shape
- C08K7/22—Expanded, porous or hollow particles
- C08K7/24—Expanded, porous or hollow particles inorganic
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L25/00—Compositions of, homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and at least one being terminated by an aromatic carbocyclic ring; Compositions of derivatives of such polymers
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- C08L25/04—Homopolymers or copolymers of styrene
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
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Abstract
The invention belongs to the technical field of biomedical materials, and discloses a tissue adhesion conductive porous hydrogel and a preparation method thereof. The method comprises the following steps: uniformly dispersing methacrylic anhydride modified gelatin and a water solution of laponite to obtain an emulsion; uniformly mixing the conductive component, the photoinitiator and the emulsion to obtain mixed emulsion; or uniformly dispersing the methacrylic anhydride modified gelatin, the laponite solution, the conductive component and the photoinitiator to obtain a mixed emulsion; carrying out ultraviolet irradiation polymerization on the mixed emulsion to obtain tissue adhesion conductive porous hydrogel; the conductive component is PEDOT PSS or CNT. The method is simple, and the prepared porous hydrogel material has good biocompatibility, tissue adhesion and electrical conductivity. And the porous hydrogel can be adhered to the surface of biological tissues in situ, so that the hemostasis and the closure of skin wounds are promoted. In addition, the invention has a mutually communicated pore structure, which is beneficial to the diffusion and permeation of substances.
Description
Technical Field
The invention belongs to the technical field of biomedical materials, and particularly relates to porous adhesive conductive hydrogel and a preparation method thereof.
Background
The formation of stable emulsions generally requires the addition of adjuvants, but these adjuvants are generally biologically toxic, making the hydrogels prepared unusable in biomedical applications. To solve this problem, it is necessary to design a template that can achieve stable emulsion without adding an auxiliary agent. Therefore, in recent years, many different mechanisms of emulsion preparation have been developed, including freeze-drying, porogen, phase separation and templating. The template method is classified into a surfactant template method and an emulsion template method.
The emulsion template method is similar to the surfactant method, firstly, an intermediate phase emulsion template is prepared, after the polymerization is successful, the intermediate phase emulsion template is separated from a continuous phase and a dispersed phase, and then the template is removed by treatment to obtain the porous hydrogel. The pore canal of the porous material is controlled by changing the relevant factors such as the type, the size, the shape and the like of the emulsion template.
However, the pore size distribution of the porous structure of the currently prepared porous hydrogel is not uniform, the pore size is difficult to control, and an organic solvent may be added in the preparation process to reduce the biocompatibility of the material. In addition, the pores of the porous hydrogel prepared by the existing method are usually closed, and the tissue growth connection and cell migration cannot be promoted.
The invention adopts an air-in-water emulsion template, and the preparation method comprises the following steps of adding Laponite (Laponite) and a conductive component PEDOT: PSS (poly (3, 4-ethylenedioxythiophene) -polystyrene sulfonate) or CNT (carbon nano tube) promotes the stability of the emulsion, improves the conductivity of the emulsion, and is beneficial to preparing porous hydrogel with good biocompatibility, tissue adhesion and conductivity. The porous hydrogel disclosed by the invention has a communicated porous structure, can effectively promote the transport of nutrient substances and the discharge of metabolic wastes, is beneficial to the inward growth of cells, and promotes the tissue repair connection.
Disclosure of Invention
In order to overcome the disadvantages and shortcomings of the prior art, the present invention aims to provide a tissue-adhesive electrically conductive porous hydrogel and a preparation method thereof. According to the invention, methacrylic anhydride modified gelatin is used as a stabilizer as an emulsion template, and the laponite and the conductive component are added, so that the prepared porous hydrogel has good biocompatibility, tissue adhesion and conductivity. And the porous hydrogel can be adhered to the surface of biological tissues in situ, and can promote the hemostasis and sealing of skin wounds.
In order to realize the purpose, the invention adopts the following technical scheme:
a preparation method of tissue adhesion conductive porous hydrogel comprises the following steps:
1) uniformly dispersing methacrylic anhydride modified gelatin (GelMA) and a laponite solution to obtain an emulsion;
2) uniformly mixing the conductive component, the photoinitiator and the emulsion, and polymerizing under ultraviolet irradiation to obtain the tissue adhesion conductive porous hydrogel; the laponite solution is laponite.
The laponite solution is a laponite water solution; laponite (Laponite) is Laponite (XLG-XR) available from BYK chemical germany.
The concentration of the laponite solution is 0.001-0.02 g/mL, namely the mass-volume ratio of the laponite to the water is (0.1-2) g: 100 mL.
The mass ratio of the methacrylic anhydride modified gelatin to the laponite is (2-20) g to (0.1-2). The mass volume ratio of the methacrylic anhydride modified gelatin to water in the emulsion is (2-20) g: 100 mL.
The mass ratio of the photoinitiator to the laponite in the step 1) is (0.2-1) g to (0.1-2).
The mass-volume ratio of the photoinitiation to the water is (0.2-1) g: 100 mL.
The mass ratio of the conductive component to the laponite in the step 1) is (0.1-3) g to (0.1-2).
The mass volume ratio of the conductive component to the water is (0.1-3) g: 100 mL.
The step 1) of uniform dispersion refers to high-speed homogeneous dispersion, wherein the rotating speed is 15000-17000 rpm, and the time of the high-speed homogeneous dispersion is 1-3 min;
the grafting rate of the methacrylic anhydride modified gelatin is 65-90% (grafting rate of methacrylic anhydride in the methacrylic anhydride modified gelatin)
The photoinitiator is 2-hydroxy-4' - (2-hydroxyethoxy) -2-methyl propiophenone (I2959) or Lithium Acyl Phosphite (LAP);
the conductive component is PEDOT: PSS (poly (3, 2-ethylenedioxythiophene) -polystyrene sulfonate) or CNT (carbon nanotubes).
The temperature during dispersion in the step 1) is 20-35 ℃;
the light intensity of the ultraviolet light in the step 2) is 50-500 mu w/cm2；
The ultraviolet irradiation time in the step 2) is 0.5-4 min.
The porosity of the porous hydrogel is 43-62%, and the pore diameter is 70-140 μm.
The porous hydrogel can be used in the fields of biomedicine and tissue engineering.
Compared with the prior art, the invention has the following advantages:
1) the invention does not use any chemical cross-linking agent and organic solvent, is beneficial to improving the safety of the material and has good biocompatibility;
2) the GelMA emulsion template adopted by the invention has high stability, can maintain the basic structure of the emulsion in the polymerization reaction and is beneficial to the formation of porous hydrogel;
3) the Laponite adopted by the invention has a promotion effect on the stability of the emulsion, and is beneficial to the stability of the emulsion and the preparation of the porous hydrogel;
4) the adhesive conductive porous hydrogel prepared by the invention has good conductivity, adhesiveness, hemostasis and mechanical properties;
5) the size, the structure and other properties of the pore channel of the adhesive conductive porous hydrogel prepared by the invention can be flexibly changed by adjusting the concentration of the Laponite and the content of the conductive component so as to meet the requirements of various applications;
6) the shape of the prepared adhesive conductive porous hydrogel can be realized by changing the shape of a die, so that the adhesive conductive porous hydrogel is convenient to adapt to the requirements of different applications;
7) the prepared adhesive conductive porous hydrogel can be adhered to the surface of biological tissue in situ, and can promote the hemostasis and closure of skin wounds;
8) the prepared adhesive conductive porous hydrogel has an open macroporous structure and high porosity, and is beneficial to diffusion and permeation of substances;
9) the preparation process of the adhesive conductive porous hydrogel is simple and easy to implement, low in raw material cost, easy for batch production and high in application and popularization values.
Drawings
FIG. 1 is an optical diagram of the pre-polymerization solution prepared in step (3) and the gel prepared in step (4) in example 3; a is prepolymerization liquid, B is gel;
FIG. 2 is a scanning electron microscope image of the internal porous structure of the adherent conductive porous hydrogel prepared in example 3;
FIG. 3 is a bar graph of conductivity tests for adherent conductive porous hydrogels prepared with varying amounts of laponite and conductive component; in the figure, Laponite represents Laponite;
FIG. 4 is a graph showing the lap shear performance of the adhesive conductive porous hydrogel prepared in examples 1 to 4, wherein 0 wt%, 0.5 wt%, 1 wt%, and 2 wt% correspond to examples 1, 2, 3, and 4, respectively;
FIG. 5 is a graph showing the test of the adhesion properties of the adhesive conductive porous hydrogel prepared in example 3; wherein A-D are adhesion performance test graphs of the adhesion conductive porous hydrogel on heart, liver, lung and kidney tissues of the pig respectively; e and F are respectively a water leakage situation diagram before and after the notch part of the hydrogel closed centrifugal tube; g and H are test charts for testing the adhesive performance of the hydrogel in air and water by using a glass slide and a weight (100G) respectively;
FIG. 6 is a blood coagulation performance test chart of the adhesive conductive porous hydrogel prepared in examples 1 to 4, wherein 0 wt%, 0.5 wt%, 1 wt%, and 2 wt% correspond to examples 1, 2, 3, and 4, respectively.
Detailed Description
The present invention will be further specifically described below with reference to specific examples, but the embodiments of the present invention are not limited thereto.
The following examples illustrate the sources of the raw materials used: PEDOT: PSS, I2959, dimethylacrylic anhydride were purchased from Siqma-Aldrich; laponite was purchased from BYK, germany.
The invention utilizes the following components of Laponite, PEDOT: the electrostatic interaction between the PSS and the GelMA promotes the uniform distribution of the PSS, the GelMA and the GelMA, stabilizes the air-in-water emulsion and enhances the crosslinking network density of the gel.
Example 1
A preparation method of porous adhesive conductive hydrogel comprises the following steps:
(1) preparing 1mL of a 0 wt% Laponite (Laponite) aqueous solution;
(2) adding 0.1g of GelMA (the concentration of GelMA in water is 10 wt%) into the step (1) to be uniformly dissolved, and intensively stirring for 2min at 16000rpm by using a high-speed dispersion homogenizer to obtain a stable emulsion;
(3) adding 0.01g of conductive component PEDOT: PSS (1 wt% in water) and 0.005g of photoinitiator I2959 (0.5 wt% in water) were dissolved uniformly;
(4) 50 mu w/cm of the mixed solution obtained in the step (3)2Irradiating with ultraviolet lamp for 2min, and performing room temperature light-initiated polymerization to obtain hydrogel.
Example 2
A preparation method of porous adhesive conductive hydrogel comprises the following steps:
(1) preparing a 0.5 wt% Laponite (Laponite) aqueous solution: 0.005g of laponite and 1mL of solvent water in volume;
(2) adding 0.1g of GelMA (with the concentration of 10 wt% in water) into the step (1) to be uniformly dissolved, and intensively stirring for 2min at 16000rpm by using a high-speed dispersion homogenizer to obtain stable emulsion;
(3) adding 0.01g of conductive component PEDOT: PSS (1 wt% in water) and 0.005g of photoinitiator I2959 (0.5 wt% in water) were dissolved uniformly;
(4) using 100 mu w/cm of the mixed solution obtained in the step (3)2Irradiating with ultraviolet lamp with light intensity for 3min, and performing room temperature light-initiated polymerization to obtain physical gel.
Example 3
A preparation method of porous adhesive conductive hydrogel comprises the following steps:
(1) preparing a 1 wt% Laponite (Laponite) solution: 0.01g of laponite and 1mL of solvent water;
(2) adding 0.1g of GelMA (with the concentration of 10 wt% in water) into the step (1) to be uniformly dissolved, and intensively stirring for 2min at 16000rpm by using a high-speed dispersion homogenizer to obtain stable emulsion;
(3) adding 0.01g of conductive component PEDOT: PSS (1 wt% in water) and 0.005g of photoinitiator I2959 (0.5 wt% in water) were dissolved uniformly;
(4) using the mixed solution obtained in the step (3) with 250 mu w/cm2Irradiating with ultraviolet lamp with light intensity for 1min, and performing room temperature light-initiated polymerization to obtain physical gel.
Example 4
A preparation method of porous conductive hydrogel comprises the following steps:
(1) preparing a 2 wt% Laponite (Laponite) solution: 0.02g of laponite and 1mL of solvent water;
(2) adding 0.1g of GelMA (with the concentration of 10 wt% in water) into the step (1) to be uniformly dissolved, and intensively stirring for 2min at 16000rpm by using a high-speed dispersion homogenizer to obtain stable emulsion;
(3) adding 0.01g of conductive component PEDOT: PSS (1 wt% in water) and 0.005g of photoinitiator I2959 (0.5 wt% in water) were dissolved uniformly;
(4) 500 mu w/cm of the mixed solution obtained in the step (3)2Irradiating with ultraviolet lamp with light intensity for 0.5min, and performing room temperature light-initiated polymerization to obtain physical gel.
Example 5
A preparation method of porous conductive hydrogel comprises the following steps:
(1) preparing a 1 wt% Laponite (Laponite) solution: 0.01g of laponite and 1mL of solvent water;
(2) adding 0.1g of GelMA (with the concentration of 10 wt% in water) into the step (1) to be uniformly dissolved, and intensively stirring for 2min at 16000rpm by using a high-speed dispersion homogenizer to obtain stable emulsion;
(3) to the mixed solution obtained before the stirring in step (2) was added 0.005g of a conductive component PEDOT: PSS (0.5 wt% in water) and 0.005g of photoinitiator I2959 (0.5 wt% in water) were dissolved uniformly;
(4) 50 mu w/cm of the mixed solution obtained in the step (3)2Irradiating with ultraviolet lamp with light intensity for 2min, and performing room temperature light-initiated polymerization to obtain physical gel.
The porosity of the gels prepared in examples 1 to 4 were 43.6%, 52.2%, 57.2%, 61.3%, respectively.
FIG. 1 is an optical diagram of the pre-polymerization solution prepared in step (3) and the gel prepared in step (4) in example 3; a is prepolymerization liquid, B is gel;
FIG. 2 is a scanning electron microscope image of the internal porous structure of the adhesive conductive porous hydrogel prepared in example 3.
FIG. 3 is a bar graph of conductivity tests for adherent conductive porous hydrogels prepared with varying amounts of laponite and conductive component; in the figure, Laponite represents Laponite; the conditions of the adhered conductive porous hydrogel in the preparation process are the same as those of example 3 except that the laponite and the conductive component are changed.
FIG. 4 is a graph showing the lap shear performance of the adhesive conductive porous hydrogel prepared in examples 1 to 4, wherein 0 wt%, 0.5 wt%, 1 wt%, and 2 wt% correspond to examples 1, 2, 3, and 4, respectively.
Lap shear testing was performed according to ASTM F2255-05 modified for tissue adhesives [ Annabi N, Rana D, Sani E S, et al].Biomaterials，2017，139∶229-243.]. Coating a 20 wt% gelatin solution on glass slides at 45 ℃, standing at room temperature and drying to form a gelatin layer of 1cm multiplied by 1cm, using a rubber circle with the diameter of 1cm for controlling the area, injecting 200 mu L of pre-polymerization emulsion (a mixed solution containing a conductive component and a photoinitiator) into the rubber circle, fixing the relative positions of the two glass slides, and using a high-intensity ultraviolet lamp (50-500 mW/cm)2) Photo-initiated polymerization is carried out for 0.5-4 minThe slides were glued together. One end of the slide was fixed using a texture analyzer and the other end was stretched at a strain rate of 1mm/min and the maximum tensile stress was recorded at the separation point.
FIG. 5 is a graph showing the test of the adhesion properties of the adhesive conductive porous hydrogel prepared in example 3; wherein A-D are adhesion performance test graphs of the adhesion conductive porous hydrogel on heart, liver, lung and kidney tissues of the pig respectively; e and F are respectively a water leakage situation diagram before and after the notch part of the hydrogel closed centrifugal tube; g and H are test charts for testing the adhesion performance of the hydrogel in air and water by using a glass slide and a weight (100G), respectively.
FIG. 6 is a blood coagulation performance test chart of the adhesive conductive porous hydrogel prepared in examples 1 to 4, wherein 0 wt%, 0.5 wt%, 1 wt%, and 2 wt% correspond to examples 1, 2, 3, and 4, respectively.
Blood coagulation performance test: rewarming fresh rabbit whole blood (sodium citrate anticoagulation) in a constant temperature shaking table at 37 ℃, cutting the gel into round pieces with the thickness of 1mm and the diameter of 10mm, sequentially rinsing with deionized water and PBS for 3 times, then putting the round pieces into a 48-hole plate after absorbing surface moisture with filter paper, and putting the round pieces in the constant temperature shaking table at 37 ℃. 30 mu L0.2M CaCl in sequence2Adding the solution and 300 mu L of fresh rabbit whole blood into a pore plate to completely immerse the gel, wherein the shaking table speed is 60r/min, sucking out the non-coagulated blood by using a suction pipe or a pipette after a period of time, adding a proper amount of PBS (phosphate buffer solution) for rinsing for 3 times, observing the coagulation condition and shooting images, and meanwhile, taking a blank group as a control.
And (4) conclusion:
as can be seen from FIG. 1, the hydrogel prepared by the air-in-water emulsion template showed decreased transparency and increased volume.
As can be seen from FIG. 2, the gel has a connected porous structure and uniform pore size distribution, with a pore size of 96.9. + -. 19.9. mu.m.
As can be seen from fig. 3, Laponite and PEDOT: the conductivity of the gel can be enhanced by increasing the concentration of the PSS.
As can be seen from FIG. 4, the lap shear strength increases with increasing Laponite concentration.
As can be seen from FIG. 5, the porous gel can effectively adhere to the heart, liver, lung, kidney and other tissues of the pig, can seal the gap of a centrifugal tube filled with water, and can have a certain adhesion effect under water.
As can be seen from fig. 6, the porous gel effectively promoted blood coagulation, and the coagulation effect was enhanced with an increase in Laponite concentration.
In the examples GelMA can be prepared by the following method:
weighing 6g of gelatin in a 100ml container, adding 60ml of phosphoric acid buffer solution, sealing the container, stirring at a constant speed of 300rpm, and dissolving in a water bath at 50 ℃ for 30min until the gelatin is completely dissolved to form a light yellow clear liquid;
adding 12ml of Methacrylic Anhydride (MA) into the solution obtained in the step (I), controlling the pH of the system to be 7.4-11.0, and controlling the dropping rate of the MA to be 4-6s one drop;
③ reacting for 5 hours, mixing the mixed solution with phosphoric acid buffer solution, mixing the mixed solution with 1: 10 volume of the mixture is mixed to terminate the reaction, the mixture is kept stand overnight to remove the precipitate; and dialyzing the reaction solution with deionized water for 7d, changing water for 2 times every day, keeping the cut-off molecular weight of the dialysis bag at 14000, taking out the liquid in the dialysis bag, and freeze-drying to obtain a foamed solid product GelMA, and hermetically storing at-20 ℃ for later use.
Claims (9)
1. A preparation method of tissue adhesion conductive porous hydrogel is characterized in that: the method comprises the following steps:
1) uniformly dispersing methacrylic anhydride modified gelatin and a laponite solution to obtain an emulsion;
2) uniformly mixing the conductive component, the photoinitiator and the emulsion to obtain mixed emulsion; carrying out ultraviolet irradiation polymerization on the mixed emulsion to obtain tissue adhesion conductive porous hydrogel; the laponite solution is an aqueous solution of laponite;
the conductive component is PEDOT: PSS or CNT.
2. The method for preparing the tissue-adhesive conductive porous hydrogel according to claim 1, wherein: the concentration of the laponite solution is 0.001-0.02 g/mL, namely the mass-volume ratio of laponite to water is (0.1-2) g: 100 mL;
the mass ratio of the methacrylic anhydride modified gelatin to the laponite is (0.02-0.2) g to (0.001-0.02) g; the mass volume ratio of the methacrylic anhydride modified gelatin to water in the emulsion is (2-20) g: 100 mL;
the mass ratio of the conductive component to the laponite in the step 1) is (0.001-0.03) g to (0.001-0.02) g.
3. The method for preparing the tissue-adhesive conductive porous hydrogel according to claim 1, wherein: the mass ratio of the photoinitiator to the laponite in the step 1) is (0.002-0.01) g to (0.001-0.02) g;
the mass volume ratio of the photoinitiation to the water is (0.2-1) g: 100 mL;
the mass volume ratio of the conductive component to the water is (0.1-3) g: 100 mL.
4. The method for preparing the tissue-adhesive conductive porous hydrogel according to claim 1, wherein: the step 1) of uniform dispersion refers to high-speed homogeneous dispersion, wherein the rotating speed is 15000-17000 rpm, and the time of the high-speed homogeneous dispersion is 1-3 min.
5. The method for preparing the tissue-adhesive conductive porous hydrogel according to claim 1, wherein: the grafting rate of the methacrylic anhydride modified gelatin is 65-90%;
the photoinitiator is 2-hydroxy-4' - (2-hydroxyethoxy) -2-methyl propiophenone or lithium acyl phosphite;
the light intensity of the ultraviolet light in the step 2) is 50-500 mu w/cm2；
The ultraviolet irradiation time in the step 2) is 0.5-4 min;
the ultraviolet illumination in the step 2) is normal-temperature ultraviolet illumination.
6. The method for preparing the tissue-adhesive conductive porous hydrogel according to claim 1, wherein:
the mixed solution in the step 2) is prepared by the following method: the preparation method comprises the following steps of uniformly dispersing methacrylic anhydride modified gelatin, a laponite solution, a conductive component and a photoinitiator.
7. A tissue-adhesive electrically conductive porous hydrogel obtained by the preparation method of any one of claims 1 to 6.
8. Use of the tissue-adhesive electrically conductive porous hydrogel of claim 7, wherein: the tissue adhesion conductive porous hydrogel is used for preparing biological tissue repair materials, biological tissue cell culture carriers or scaffolds.
9. Use of the tissue-adhesive electrically conductive porous hydrogel of claim 7, wherein:
the tissue-adhesive conductive porous hydrogel is used for preparing wound dressings.
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