CN111821516B - Adhesive conductive hydrogel and preparation method and application thereof - Google Patents
Adhesive conductive hydrogel and preparation method and application thereof Download PDFInfo
- Publication number
- CN111821516B CN111821516B CN202010379799.5A CN202010379799A CN111821516B CN 111821516 B CN111821516 B CN 111821516B CN 202010379799 A CN202010379799 A CN 202010379799A CN 111821516 B CN111821516 B CN 111821516B
- Authority
- CN
- China
- Prior art keywords
- solution
- preparation
- dopamine
- catechol
- hydrogel
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- 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
- A61L27/14—Macromolecular materials
- A61L27/26—Mixtures of macromolecular compounds
-
- 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
-
- 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
- A61L27/52—Hydrogels or hydrocolloids
-
- 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
- A61L27/54—Biologically active materials, e.g. therapeutic substances
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08B—POLYSACCHARIDES; DERIVATIVES THEREOF
- C08B37/00—Preparation of polysaccharides not provided for in groups C08B1/00 - C08B35/00; Derivatives thereof
- C08B37/0006—Homoglycans, i.e. polysaccharides having a main chain consisting of one single sugar, e.g. colominic acid
- C08B37/0024—Homoglycans, i.e. polysaccharides having a main chain consisting of one single sugar, e.g. colominic acid beta-D-Glucans; (beta-1,3)-D-Glucans, e.g. paramylon, coriolan, sclerotan, pachyman, callose, scleroglucan, schizophyllan, laminaran, lentinan or curdlan; (beta-1,6)-D-Glucans, e.g. pustulan; (beta-1,4)-D-Glucans; (beta-1,3)(beta-1,4)-D-Glucans, e.g. lichenan; Derivatives thereof
- C08B37/0027—2-Acetamido-2-deoxy-beta-glucans; Derivatives thereof
- C08B37/003—Chitin, i.e. 2-acetamido-2-deoxy-(beta-1,4)-D-glucan or N-acetyl-beta-1,4-D-glucosamine; Chitosan, i.e. deacetylated product of chitin or (beta-1,4)-D-glucosamine; Derivatives thereof
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G73/00—Macromolecular compounds obtained by reactions forming a linkage containing nitrogen with or without oxygen or carbon in the main chain of the macromolecule, not provided for in groups C08G12/00 - C08G71/00
- C08G73/06—Polycondensates having nitrogen-containing heterocyclic rings in the main chain of the macromolecule
- C08G73/0605—Polycondensates containing five-membered rings, not condensed with other rings, with nitrogen atoms as the only ring hetero atoms
- C08G73/0611—Polycondensates containing five-membered rings, not condensed with other rings, with nitrogen atoms as the only ring hetero atoms with only one nitrogen atom in the ring, e.g. polypyrroles
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G73/00—Macromolecular compounds obtained by reactions forming a linkage containing nitrogen with or without oxygen or carbon in the main chain of the macromolecule, not provided for in groups C08G12/00 - C08G71/00
- C08G73/06—Polycondensates having nitrogen-containing heterocyclic rings in the main chain of the macromolecule
- C08G73/0666—Polycondensates containing five-membered rings, condensed with other rings, with nitrogen atoms as the only ring hetero atoms
- C08G73/0672—Polycondensates containing five-membered rings, condensed with other rings, with nitrogen atoms as the only ring hetero atoms with only one nitrogen atom in the ring
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G81/00—Macromolecular compounds obtained by interreacting polymers in the absence of monomers, e.g. block polymers
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J3/00—Processes of treating or compounding macromolecular substances
- C08J3/02—Making solutions, dispersions, lattices or gels by other methods than by solution, emulsion or suspension polymerisation techniques
- C08J3/03—Making solutions, dispersions, lattices or gels by other methods than by solution, emulsion or suspension polymerisation techniques in aqueous media
- C08J3/075—Macromolecular gels
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J3/00—Processes of treating or compounding macromolecular substances
- C08J3/24—Crosslinking, e.g. vulcanising, of macromolecules
- C08J3/246—Intercrosslinking of at least two polymers
-
- D—TEXTILES; PAPER
- D01—NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
- D01F—CHEMICAL FEATURES IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS; APPARATUS SPECIALLY ADAPTED FOR THE MANUFACTURE OF CARBON FILAMENTS
- D01F8/00—Conjugated, i.e. bi- or multicomponent, artificial filaments or the like; Manufacture thereof
- D01F8/04—Conjugated, i.e. bi- or multicomponent, artificial filaments or the like; Manufacture thereof from synthetic polymers
- D01F8/16—Conjugated, i.e. bi- or multicomponent, artificial filaments or the like; Manufacture thereof from synthetic polymers with at least one other macromolecular compound obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds as constituent
-
- 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
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
- A61L2300/252—Polypeptides, proteins, e.g. glycoproteins, lipoproteins, cytokines
-
- 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
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
- A61L2300/412—Tissue-regenerating or healing or proliferative agents
-
- 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
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/20—Materials or treatment for tissue regeneration for reconstruction of the heart, e.g. heart valves
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2305/00—Characterised by the use of polysaccharides or of their derivatives not provided for in groups C08J2301/00 or C08J2303/00
- C08J2305/08—Chitin; Chondroitin sulfate; Hyaluronic acid; Derivatives thereof
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2387/00—Characterised by the use of unspecified macromolecular compounds, obtained otherwise than by polymerisation reactions only involving unsaturated carbon-to-carbon bonds
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2405/00—Characterised by the use of polysaccharides or of their derivatives not provided for in groups C08J2401/00 or C08J2403/00
- C08J2405/08—Chitin; Chondroitin sulfate; Hyaluronic acid; Derivatives thereof
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2479/00—Characterised by the use of macromolecular compounds obtained by reactions forming in the main chain of the macromolecule a linkage containing nitrogen with or without oxygen, or carbon only, not provided for in groups C08J2461/00 - C08J2477/00
- C08J2479/04—Polycondensates having nitrogen-containing heterocyclic rings in the main chain; Polyhydrazides; Polyamide acids or similar polyimide precursors
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2487/00—Characterised by the use of unspecified macromolecular compounds, obtained otherwise than by polymerisation reactions only involving unsaturated carbon-to-carbon bonds
Abstract
The invention provides an adhesive conductive hydrogel and a preparation method and application thereof, belonging to the field of biomedical engineering materials. The dopamine-polypyrrole nano-fiber, the catechol-modified chitosan and the cyclodextrin grafted gelatin are dissolved in water, and the ferric chloride solution is added for crosslinking to obtain the adhesive conductive hydrogel, wherein the dopamine-polypyrrole nano-fiber, the catechol-modified chitosan and the cyclodextrin grafted gelatin are uniformly dispersed and fixed in a hydrogel network in the hydrogel, so that the hydrogel is endowed with good biocompatibility and conductivity, and meanwhile, the catechol-modified chitosan is endowed with good viscosity, so that the matrix cell derived factor SDF-1 is loaded, the retention effect of the SDF-1 in vivo can be enhanced, and the SDF-1 is prevented from losing efficacy too fast.
Description
Technical Field
The invention belongs to the field of biomedical engineering materials, and relates to an adhesive conductive hydrogel and a preparation method and application thereof.
Background
The incidence rate of acute myocardial infarction is high, and is increased by 50 thousands of cases every year, which is a main global health problem. Myocardial infarction, which usually occurs as a result of plaque rupture and thrombosis, blocks coronary arteries and results in ischemic damage to heart tissue. Adult mammals have a limited ability to regenerate the heart and ischemic injury to the cardiomyocytes is usually replaced by fibrotic scar tissue. For advanced patients, the only viable option is whole heart transplantation. However, the deficiency of the donor heart makes it difficult for most patients to get timely treatment.
Preclinical and clinical studies have shown that cell therapy can alleviate the development of myocardial injury and heart failure, but the specific mechanisms have not been elucidated. In addition to ischemic heart diseases, cell therapy is also effective for non-ischemic heart diseases such as left ventricular hypertrophy and non-ischemic dilated cardiomyopathy caused by excessive pressure load, and the clinical effects of cell transplantation therapy are limited by the low cell transplantation rate. Tissue engineered hearts are morphologically and functionally similar to natural cardiac muscle, and hydrogels are currently the most commonly used class of materials for constructing tissue engineered hearts. Various animal myocardial infarction models have proved that the development of left ventricular remodeling after infarction can be stopped to a certain extent only by simply applying hydrogel, and normal cardiac function is recovered.
The contraction of the myocardium is driven by an electrical shock wave (generated by the pacing cells) that rapidly spreads along the cell membranes of adjacent cardiomyocytes and triggers the release of calcium, which in turn stimulates the contraction of myofibrils. The electromechanical coupling of muscle cells is critical to their synchronous response to electronic pacing signals, resulting in contractile function and blood pumping. When acute myocardial infarction occurs and the damaged myocardium is replaced by fibrosis scar tissue, the conduction of myocardial electrical signals is blocked, the electromechanical coupling of myocytes is destroyed, and the myocardial contractility is weakened. On the basis, the long-term development can cause compensatory myocardial hypertrophy and finally turn into chronic heart failure, thus threatening the life of a patient. In order to enhance the electrical conductivity of the fibrotic scar tissue area, some hydrogels with electrical conductivity have been used for research. Conductive polymers (such as polypyrrole and polyaniline) have high conductivity and good electrical stability, and are widely used for the construction of conductive hydrogels. However, at present, it is difficult to find a balance between high conductivity and biocompatibility, and the conducting polymer is difficult to dissolve in water, and how to uniformly disperse the conducting polymer in the hydrogel is also an important problem to be solved.
Mesenchymal stem cells are the most commonly used cells in cardiac preclinical, especially clinical studies. These cells are defined as pluripotent, autophagic and low immunogenic and do not persist in the target tissue for long periods of time, which reduces the risk of any long-term complications after administration, but also affects the efficiency of treatment. 143 clinical studies have shown that allogeneic mesenchymal stem cells and autologous mesenchymal stem cells can both enhance cardiac function of patients with ischemic cardiomyopathy and reduce left ventricular remodeling. By injecting different doses of cells, researchers found that low doses of mesenchymal stem cells (2000 million cells) minimized left ventricular volume and increased ejection fraction compared to medium (1 million cells) or high (2 million cells). After myocardial infarction, various stem/progenitor cells in the organism can be attracted by stromal cell derived factor 1 (SDF-1) to home to the infarct area, and are differentiated into myocardial or vascular cells, and meanwhile, various endocrine factors are released, the microenvironment of the infarct area is improved, apoptosis is inhibited, and tissue repair is promoted. Unfortunately, SDF-1 α is released in limited amounts and is retained for a short period of time and thus has poor repair ability to compensate for ventricular remodeling caused by loss of cardiomyocytes and myocardial infarction.
Disclosure of Invention
In order to overcome the above disadvantages and shortcomings of the prior art, the present invention aims to provide an adhesive conductive hydrogel, a preparation method and an application thereof, so as to improve the stability of polypyrrole in an aqueous solution, the biocompatibility in vivo and the dispersibility in a hydrogel network, prepare a hydrogel with good conductivity and biocompatibility, improve the phenomenon of asynchronous electric signal conduction in a myocardial infarction region, and recruit stem cells in blood by using a stromal cell derived factor SDF-1 released at an infarction part to promote tissue repair.
In order to achieve the purpose, the invention adopts the technical scheme that:
in a first aspect, a method for preparing an adherable conductive hydrogel comprises the steps of: adding dopamine-polypyrrole nano-fibers (DA-PPY), catechol modified chitosan (Chi-C) and cyclodextrin grafted gelatin (beta-CD-Gel) into water, completely dissolving and uniformly mixing, and adding a ferric trichloride solution for crosslinking reaction to obtain the hydrogel. The dopamine-polypyrrole nano-fiber has good biocompatibility, and the dopamine-polypyrrole nano-fiber adopts dopamine to modify polypyrrole so that the dopamine-polypyrrole nano-fiber has good biocompatibility and good stability in an aqueous solution, so that the prepared hydrogel has good biocompatibility; the dopamine-polypyrrole nano fibers and the catechol modified chitosan both contain catechol groups, and the dopamine-polypyrrole nano fibers can be uniformly dispersed and fixed in a hydrogel network under the crosslinking of iron ions, so that the hydrogel is endowed with high conductivity; meanwhile, the catechol modified chitosan can enhance the adhesive capacity of the hydrogel to biological tissues, thereby avoiding the extrusion of the hydrogel after injection and enhancing the application of the hydrogel in medical clinic.
As a preferred embodiment of the preparation method of the present invention, the mass ratio of the dopamine-polypyrrole nanofiber, the catechol-modified chitosan, and the cyclodextrin-grafted gelatin is dopamine-polypyrrole nanofiber: catechol-modified chitosan: the ratio of the water for dissolving the dopamine-polypyrrole nano-fibers, the catechol modified chitosan and the cyclodextrin grafted gelatin to the ferric chloride solution is 9: 1.
as a further preferable embodiment of the preparation method of the present invention, the mass ratio of the dopamine-polypyrrole nanofiber, the catechol-modified chitosan, and the cyclodextrin-grafted gelatin is dopamine-polypyrrole nanofiber: catechol-modified chitosan: cyclodextrin grafted gelatin 0.25-1: 10-60: 50.
as a preferred embodiment of the preparation method of the present invention, the mass ratio of the dopamine-polypyrrole nanofiber, the catechol-modified chitosan, and the cyclodextrin-grafted gelatin is dopamine-polypyrrole nanofiber: catechol-modified chitosan: cyclodextrin grafted gelatin ═ 1: 40: 50.
as a preferred embodiment of the production method of the present invention, the concentration of the ferric trichloride solution is 20 mM.
As a preferred embodiment of the preparation method of the present invention, the cyclodextrin grafted gelatin is prepared by the steps of:
carboxymethylation of beta-cyclodextrin (beta-CD-COOCH)3) Dissolving 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride and N-hydroxysuccinimide in a solvent A respectively, mixing, and stirring to obtain a solution F;
under the heating condition, completely dissolving gelatin in a solvent B to obtain a solution G, adding the solution F into the solution G for reaction, dialyzing and drying after the reaction is finished to obtain the cyclodextrin grafted gelatin.
In a preferred embodiment of the preparation method of the present invention, the solvent a is a PBS solution having a pH of 7.2 to 7.4.
In a preferred embodiment of the preparation method of the present invention, the solvent B is a PBS solution having a pH of 7.2 to 7.4.
As a preferred embodiment of the preparation method of the present invention, the carboxymethylated beta-cyclodextrin, 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride and N-hydroxysuccinimide are mixed and stirred for 1 hour.
As a preferred embodiment of the production method of the present invention, the mass ratio of the carboxymethylated β -cyclodextrin, 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride, N-hydroxysuccinimide and gelatin is carboxymethylated β -cyclodextrin: 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride: n-hydroxysuccinimide: gelatin 1.135: 0.765: 0.23: 2; the volume ratio of the solution F to the solution G is that of the solution F: solution G ═ 2: 3.
As a preferred embodiment of the preparation method of the invention, the reaction of the solution F and the solution G is carried out under magnetic stirring, the rotation speed of the magnetic stirring is 500-800rpm/min, the reaction temperature is 40 ℃, and the reaction time is 12-18 h; as a further preferable embodiment of the preparation method of the present invention, the rotation speed of the magnetic stirring is 700rpm/min, and the reaction time of the magnetic stirring is 15 hours.
As a further preferred embodiment of the preparation method of the present invention, the dialysis is performed in deionized water having a pH of 5 using a dialysis bag, the molecular weight cut-off of the dialysis bag is 3500 dalton, and the dialysis time is 3 days.
As a preferred embodiment of the preparation method of the present invention, the dopamine-polypyrrole nanofiber is prepared by the following steps:
dissolving dopamine hydrochloride in hydrochloric acid, placing the solution in an ice bath, and then dropwise adding a pyrrole monomer to obtain a solution A;
dissolving ferric trichloride in hydrochloric acid to obtain a solution B;
and dropwise adding the solution B into the solution A, stirring in an ice bath, carrying out solid-liquid separation, collecting solids and washing to obtain the dopamine-polypyrrole nano-fiber.
As a preferred embodiment of the preparation method of the present invention, in the preparation step of the dopamine-polypyrrole nanofiber, the ratio of dopamine hydrochloride, ferric chloride and pyrrole monomer is dopamine hydrochloride: ferric chloride: pyrrole monomer 0.05-0.2 g: 0.5-1.0 g: 236 mu L; as a further preferred embodiment of the preparation method of the present invention, in the preparation step of the dopamine-polypyrrole nanofiber, the ratio of dopamine hydrochloride, ferric chloride and pyrrole monomer is dopamine hydrochloride: ferric chloride: pyrrole monomer 0.103 g: 0.8 g: 236. mu.L.
As a preferred embodiment of the preparation method of the present invention, the catechol-modified chitosan is prepared by the following steps:
completely dissolving chitosan (Chi) in hydrochloric acid, and adjusting the pH value to 4.0-5.0 to obtain a solution C;
dissolving 3, 4-dihydroxyphenyl propionic acid in water to obtain a solution D;
dissolving 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride in a mixed solution of ethanol and water to obtain a solution E;
and mixing the solution D and the solution E, immediately adding the mixture into the solution C, reacting, controlling the pH value of a reaction solution to be 4-5, dialyzing and drying after the reaction is finished, and obtaining the catechol modified chitosan.
As a preferred embodiment of the preparation method of the present invention, in the step of preparing the catechol-modified chitosan, the mass ratio of chitosan, 3, 4-dihydroxylpropanoic acid, and 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride is chitosan: 3, 4-dihydroxyphenyl propionic acid: 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride 0.5: 0.145: 0.31.
as a preferred embodiment of the preparation method of the invention, in the step of preparing the catechol-modified chitosan, the reaction is carried out under magnetic stirring, the rotation speed of the magnetic stirring is 500-800rpm/min, and the reaction time is 12-18 h; in a further preferred embodiment of the preparation method of the present invention, in the step of preparing the catechol-modified chitosan, the rotation speed of the magnetic stirring is 700rpm/min, and the reaction time is 15 hours.
In a further preferred embodiment of the preparation method of the present invention, in the step of preparing catechol-modified chitosan, dialysis is performed in deionized water with pH 5 using a dialysis bag, wherein the molecular weight cut-off of the dialysis bag is 3500 dalton, and the dialysis time is 3 days.
In a second aspect, the invention provides a hydrogel prepared by the preparation method.
In a third aspect, the invention also provides application of the hydrogel in repairing infarcted myocardium.
As a preferred embodiment of the application of the invention, the hydrogel loads the stromal cell derived factor SDF-1. The stromal cell derived factor SDF-1 can collect various stem/progenitor cells in vivo to home to the infarct area, differentiate into myocardial cells or vascular cells, release various endocrine factors, improve the microenvironment of the infarct area, inhibit apoptosis and promote the repair of tissues. SDF-1 is loaded in the hydrogel and reaches an infarct area in an in-situ injection mode, the release of the SDF-1 is realized at the heart stem part, the electric signal conduction of a scar area is enhanced, the infarct area is reduced, the myocardial fibrosis degree is inhibited, the retention effect of the SDF-1 in a body can be enhanced, and the problem of too fast failure is avoided.
Compared with the prior art, the invention has the following advantages and beneficial effects: the invention prepares hydrogel with good biocompatibility and conductivity by improving the stability of polypyrrole in aqueous solution, the biocompatibility in vivo and the dispersibility in a hydrogel network, and the hydrogel is loaded with the matrix cell derived factor SDF-1, so that the retention effect of the SDF-1 in vivo can be enhanced, and the failure of the SDF-1 is prevented from being too fast.
Drawings
Fig. 1 is an infrared spectrum and a nuclear magnetic resonance hydrogen spectrum of catechol-modified chitosan and cyclodextrin-grafted gelatin prepared according to the present invention, wherein fig. 1A is an infrared spectrum of 3, 4-dihydroxyphenyl propionic acid, chitosan and catechol-modified chitosan prepared according to the present invention, fig. 1B is an infrared spectrum of β -cyclodextrin, gelatin and cyclodextrin-grafted gelatin prepared according to the present invention, fig. 1C is a nuclear magnetic resonance hydrogen spectrum of catechol-modified chitosan prepared according to the present invention, and fig. 1D is a nuclear magnetic resonance hydrogen spectrum of cyclodextrin-grafted gelatin prepared according to the present invention;
FIG. 2 is a Transmission Electron Microscope (TEM) image of the dopamine-polypyrrole nanofiber prepared by the present invention;
FIG. 3 is a test of adhesion of hydrogels of different raw material ratios;
FIG. 4 is a rheological characterization of a hydrogel made according to the present invention;
FIG. 5 is a Scanning Electron Microscope (SEM) image of a hydrogel with different concentrations of dopamine-polypyrrole nanofibers added;
FIG. 6 is a photograph showing that the hydrogel prepared by the present invention makes a light emitting diode emit light.
Detailed Description
To better illustrate the objects, aspects and advantages of the present invention, the present invention will be further described with reference to specific examples.
Example 1: preparation of adhesive conductive hydrogel
(1) Preparation of dopamine-polypyrrole nano-fibers
Dissolving 0.103g of dopamine hydrochloride in 20mL of 1M hydrochloric acid, placing the solution in an ice bath, and then dropwise adding 236 mu L of pyrrole monomer to obtain a solution A;
dissolving 0.8g of ferric trichloride in 5mL of 1M hydrochloric acid, dropwise adding the solution A into the solution A, stirring in an ice bath for 12 hours, and sequentially carrying out precipitation, centrifugation and deionized water washing for three times to obtain the dopamine-polypyrrole nano fiber. A TEM image of the dopamine-polypyrrole nanofiber is shown in fig. 2;
(2) preparation of catechol modified chitosan
Dissolving 0.5g of chitosan in 50mL of 0.1M hydrochloric acid, and adjusting the pH value to 4.0-5.0 by using 1M sodium hydroxide solution to obtain solution C;
dissolving 0.145g of 3, 4-dihydroxyphenyl propionic acid in 3mL of water to obtain a solution D;
dissolving 0.31g of 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride in 50mL of mixed solution of ethanol and water (the volume ratio of the ethanol to the water is 1:1) to obtain solution E;
and mixing the solution D and the solution E, immediately adding the mixture into the solution C, magnetically stirring the mixture for 15 hours at room temperature and at the rotating speed of 700rpm/min, controlling the pH value of the reaction solution to be 4-5, after the reaction is finished, placing the reaction solution into a cellulose dialysis bag (with the molecular weight cut-off of 3500), placing the cellulose dialysis bag into deionized water (prepared by adjusting the pH value of the deionized water to be 5 through 1M hydrochloric acid) with the pH value of 5 for dialysis for 3 days, and then carrying out freeze drying at the temperature of-80 ℃ to obtain the catechol-modified chitosan. The infrared spectrum and nuclear magnetic resonance hydrogen spectrum of catechol-modified chitosan are respectively shown in FIG. 1A and FIG. 1C (HCA in FIG. 1A represents 3, 4-dihydroxylpropanoic acid);
(3) preparation of cyclodextrin grafted gelatin
Firstly, dissolving 1.135g of carboxymethylated beta-cyclodextrin in 10mL of PBS solution, dissolving 0.765g of 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride in 5mL of PBS solution, dissolving 0.23g N-hydroxysuccinimide in 5mL of PBS solution, mixing the three solutions, and stirring for 1h to obtain a solution F;
completely dissolving 2.0G of gelatin in 30mL of PBS (phosphate buffer solution) with the pH value of 7.4 in a water bath at 40 ℃ to obtain a solution G, adding the solution G into the solution F in the water bath at 40 ℃, magnetically stirring at 700rpm/min for 15 hours, placing the reaction solution into a cellulose dialysis bag (molecular weight cut-off 3500), placing the cellulose dialysis bag into deionized water with the pH value of 5 (prepared by adjusting the pH value of the deionized water to 5 by 1M hydrochloric acid) for dialysis for 3 days, and then freeze-drying at-80 ℃ to obtain the cyclodextrin grafted gelatin. The infrared spectrum and nuclear magnetic resonance hydrogen spectrum of the cyclodextrin grafted gelatin are respectively shown in FIG. 1B and FIG. 1D (in FIG. 1B, beta-CD represents beta-cyclodextrin);
(4) preparation of hydrogels
Dissolving 1mg of dopamine-polypyrrole nano-fiber, 0.04g of catechol modified chitosan and 0.05g of cyclodextrin grafted gelatin in 0.9mL of deionized water, completely dissolving and uniformly mixing, and adding 0.1mL of 20mM ferric trichloride solution for crosslinking to obtain the hydrogel. The SEM image of the hydrogel is shown in FIG. 5, and the electrical conductivity is shown in Table 1.
TABLE 1 hydrogel conductivity
Example 2: preparation of adhesive conductive hydrogel
(1) Preparation of dopamine-polypyrrole nano-fibers
The same as example 1;
(2) preparation of catechol modified chitosan
The same as example 1;
(3) preparation of cyclodextrin grafted gelatin
The same as example 1;
(4) preparation of hydrogels
Dissolving 0.5mg of dopamine-polypyrrole nano-fibers, 0.04g of catechol modified chitosan and 0.05g of cyclodextrin grafted gelatin in 0.9mL of deionized water, completely dissolving and uniformly mixing, and adding 0.1mL of 20mM ferric trichloride solution for crosslinking to obtain the hydrogel. The SEM image of the hydrogel is shown in fig. 5, and the conductivity is shown in table 1.
Example 3: preparation of adhesive conductive hydrogel
(1) Preparation of dopamine-polypyrrole nano-fibers
The same as example 1;
(2) preparation of catechol modified chitosan
The same as example 1;
(3) preparation of cyclodextrin grafted gelatin
The same as example 1;
(4) preparation of hydrogels
Dissolving 0.25mg of dopamine-polypyrrole nano-fibers, 0.04g of catechol modified chitosan and 0.05g of cyclodextrin grafted gelatin in 0.9mL of deionized water, completely dissolving and uniformly mixing, and adding 0.1mL of 20mM ferric trichloride solution for crosslinking to obtain the hydrogel. The SEM image of the hydrogel is shown in fig. 5, and the conductivity is shown in table 1.
Example 4: preparation of hydrogels
(1) Preparation of catechol modified chitosan
The same as example 1;
(2) preparation of cyclodextrin grafted gelatin
The same as example 1;
(3) preparation of hydrogels
0.01g of catechol-modified chitosan and 0.05g of cyclodextrin grafted gelatin are dissolved in 0.9mL of deionized water, and after complete dissolution and uniform mixing, 0.1mL of 20mM ferric chloride solution is added for crosslinking, thus obtaining the hydrogel. The lap tensile test results for this hydrogel are shown in fig. 3, and the rheological characterization is shown in fig. 4.
Example 5: preparation of hydrogels
(1) Preparation of catechol modified chitosan
The same as example 1;
(2) preparation of cyclodextrin grafted gelatin
The same as example 1;
(3) preparation of hydrogels
0.02g of catechol-modified chitosan and 0.05g of cyclodextrin grafted gelatin are dissolved in 0.9mL of deionized water, and after complete dissolution and uniform mixing, 0.1mL of 20mM ferric chloride solution is added for crosslinking, thus obtaining the hydrogel. The shear stress test results of the hydrogel are shown in fig. 3, and the rheological property characterization is shown in fig. 4.
Example 6: preparation of hydrogels
(1) Preparation of catechol modified chitosan
The same as example 1;
(2) preparation of cyclodextrin grafted gelatin
The same as example 1;
(3) preparation of hydrogels
0.04g of catechol-modified chitosan and 0.05g of cyclodextrin grafted gelatin are dissolved in 0.9mL of deionized water, and after complete dissolution and uniform mixing, 0.1mL of 20mM ferric chloride solution is added for crosslinking, thus obtaining the hydrogel. The shear stress test results of the hydrogel are shown in fig. 3, and the rheological property characterization is shown in fig. 4.
Example 7: preparation of hydrogels
(1) Preparation of catechol modified chitosan
The same as example 1;
(2) preparation of cyclodextrin grafted gelatin
The same as example 1;
(3) preparation of hydrogels
0.06g of catechol-modified chitosan and 0.05g of cyclodextrin grafted gelatin are dissolved in 0.9mL of deionized water, and after complete dissolution and uniform mixing, 0.1mL of 20mM ferric chloride solution is added for crosslinking, thus obtaining the hydrogel. The shear stress test results of the hydrogel are shown in fig. 3, and the rheological property characterization is shown in fig. 4.
On the basis of the embodiments 4 to 7, the invention also uses dopamine-polypyrrole nano-fibers when preparing the hydrogel, so that the prepared hydrogel not only can keep good adhesion capability, but also has good conductivity and biocompatibility; in addition, the preparation method of the adhesive conductive hydrogel has the same change trend of the shear stress and the rheological property of the hydrogel in the embodiments 4-7 under the condition that the dosage of the catechol modified chitosan is only changed.
It should be finally noted that the above embodiments are only intended to illustrate the technical solutions of the present invention and not to limit the scope of the present invention, and although the present invention has been described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that modifications or equivalent substitutions may be made on the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention.
Claims (10)
1. A preparation method of an adhesive conductive hydrogel is characterized by comprising the following steps: adding dopamine-polypyrrole nano-fibers, catechol modified chitosan and cyclodextrin grafted gelatin into water, completely dissolving and uniformly mixing, and adding a ferric trichloride solution for crosslinking reaction to obtain the hydrogel.
2. The preparation method according to claim 1, wherein the mass ratio of the dopamine-polypyrrole nano-fibers, the catechol-modified chitosan and the cyclodextrin grafted gelatin is dopamine-polypyrrole nano-fibers: catechol-modified chitosan: cyclodextrin grafted gelatin 0.1-2:10-60:50, the concentration of the ferric trichloride solution is 10-100mM, and the volume ratio of water for dissolving the dopamine-polypyrrole nano fibers, the catechol modified chitosan and the cyclodextrin grafted gelatin to the ferric trichloride solution is 9: 1.
3. The preparation method according to claim 2, wherein the mass ratio of the dopamine-polypyrrole nano-fibers, the catechol-modified chitosan and the cyclodextrin grafted gelatin is dopamine-polypyrrole nano-fibers: catechol-modified chitosan: cyclodextrin grafted gelatin 0.25-1: 10-60:50, and the concentration of the ferric trichloride solution is 20 mM.
4. The method of claim 1, wherein the cyclodextrin grafted gelatin is prepared by the steps of:
dissolving carboxymethylated beta-cyclodextrin, 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride and N-hydroxysuccinimide in a solvent A respectively, mixing, and stirring to obtain a solution F;
under the heating condition, completely dissolving gelatin in a solvent B to obtain a solution G, adding the solution F into the solution G for reaction, dialyzing and drying after the reaction is finished to obtain the cyclodextrin grafted gelatin.
5. The preparation method according to claim 4, wherein in the cyclodextrin grafted gelatin preparation step, the solvent A and the solvent B are both PBS solutions with pH values of 7.2-7.4; the mass ratio of the carboxymethylated beta-cyclodextrin to the 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride to the N-hydroxysuccinimide to the gelatin is as follows: 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride: n-hydroxysuccinimide: gelatin 1.135: 0.765: 0.23: 2; the volume ratio of the solution F to the solution G is that of the solution F: solution G ═ 2: 3; the reaction of the solution F and the solution G is carried out under the magnetic stirring, the rotating speed of the magnetic stirring is 500-800rpm/min, the reaction temperature is 40 ℃, and the reaction time is 12-18 h; the dialysis is carried out in deionized water with pH value of 5 by adopting a dialysis bag, and the molecular weight cut-off of the dialysis bag is 3500 Dalton.
6. The preparation method according to claim 1, wherein the dopamine-polypyrrole nano-fibers are prepared by the following steps:
dissolving dopamine hydrochloride in hydrochloric acid, placing the solution in an ice bath, and then dropwise adding a pyrrole monomer to obtain a solution A;
dissolving ferric trichloride in hydrochloric acid to obtain a solution B;
and dropwise adding the solution B into the solution A, stirring in an ice bath, carrying out solid-liquid separation, collecting solids and washing to obtain the dopamine-polypyrrole nano-fiber.
7. The method according to claim 1, wherein the catechol-modified chitosan is prepared by the following steps:
completely dissolving chitosan in hydrochloric acid, and adjusting the pH value to 4.0-5.0 to obtain a solution C;
dissolving 3, 4-dihydroxyphenyl propionic acid in water to obtain a solution D;
dissolving 1-ethyl- (3-dimethylaminopropyl) carbodiimide hydrochloride in a mixed solution of ethanol and water to obtain a solution E;
and mixing the solution D and the solution E, immediately adding the mixture into the solution C, reacting, controlling the pH value of a reaction solution to be 4-5, dialyzing and drying after the reaction is finished, and obtaining the catechol modified chitosan.
8. A hydrogel produced by the production method according to any one of claims 1 to 7.
9. Use of a hydrogel according to claim 8 for the preparation of a product for the repair of infarcted myocardium.
10. The use according to claim 9, wherein the hydrogel supports the stromal cell derived factor SDF-1.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010379799.5A CN111821516B (en) | 2020-05-07 | 2020-05-07 | Adhesive conductive hydrogel and preparation method and application thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010379799.5A CN111821516B (en) | 2020-05-07 | 2020-05-07 | Adhesive conductive hydrogel and preparation method and application thereof |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN111821516A CN111821516A (en) | 2020-10-27 |
| CN111821516B true CN111821516B (en) | 2021-12-24 |
Family
ID=72913882
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202010379799.5A Active CN111821516B (en) | 2020-05-07 | 2020-05-07 | Adhesive conductive hydrogel and preparation method and application thereof |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN111821516B (en) |
Families Citing this family (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113069594B (en) * | 2021-04-02 | 2022-12-06 | 广东工业大学 | Supermolecule hydrogel and preparation method and application thereof |
| CN113292723B (en) * | 2021-04-12 | 2022-04-08 | 浙江大学 | Preparation method of morphology-controllable polypyrrole conductive nano material |
| CN113503991B (en) * | 2021-04-12 | 2022-12-09 | 浙江大学 | High-sensitivity piezoresistive sensor based on dopamine-modified polypyrrole conductive hydrogel and preparation method thereof |
| CN113563609A (en) * | 2021-07-28 | 2021-10-29 | 华南理工大学 | Nano composite porous hydrogel and preparation and application thereof |
| CN114306751B (en) * | 2021-12-30 | 2022-11-11 | 智享生物(苏州)有限公司 | Multifunctional nanofiber scaffold for improving cell adhesion and preparation method thereof |
| CN114477845A (en) * | 2022-03-21 | 2022-05-13 | 辛集慕湖混凝土有限公司 | Cement grinding aid and preparation method thereof |
| CN114854160B (en) * | 2022-04-14 | 2023-03-10 | 山东大学 | Conductive hydrogel based on water-soluble polypyrrole and preparation method thereof |
| CN114773630A (en) * | 2022-05-24 | 2022-07-22 | 湖北工业大学 | Photo-thermal sterilization adhesive hydrogel and preparation method and application thereof |
| CN115010998B (en) * | 2022-06-10 | 2022-12-06 | 西安交通大学 | Antibacterial antioxidant conductive adhesive hydrogel and preparation method and application thereof |
| CN115521508B (en) * | 2022-10-27 | 2023-09-05 | 四川大学 | Particle-free homogeneous conductive hydrogel and preparation method and application thereof |
| CN116004046B (en) * | 2023-02-07 | 2023-10-20 | 上海正欧实业有限公司 | Anticorrosive microparticle, application thereof, anticorrosive polyurethane floor coating and preparation method thereof |
| CN115957181B (en) * | 2023-02-08 | 2023-09-15 | 江苏省人民医院（南京医科大学第一附属医院） | Injectable thermosensitive hydrogel suitable for myocardial infarction repair and preparation method thereof |
| CN116350835B (en) * | 2023-03-24 | 2023-09-15 | 中国海洋大学 | Biological hemostatic sponge and preparation method thereof |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2014121378A1 (en) * | 2013-02-05 | 2014-08-14 | University Health Network | Conductive biomaterial for enhancement of conduction in vitro and in vivo |
| CN105906821A (en) * | 2016-04-26 | 2016-08-31 | 西南交通大学 | Preparation method of self-adhesion electroconductive hydrogel |
| CN108467498A (en) * | 2018-06-12 | 2018-08-31 | 华中科技大学 | A kind of supramolecular hydrogel and the preparation method and application thereof of chitosan and gelatin |
| CN109456444A (en) * | 2018-10-22 | 2019-03-12 | 西南交通大学 | A kind of preparation method for sticking conductive hydrogel for tissue repair |
| CN109575318A (en) * | 2018-11-16 | 2019-04-05 | 华南理工大学 | A kind of polypyrrole conductive hydrogel of DA Mediated and preparation method thereof |
| CN109627461A (en) * | 2018-11-21 | 2019-04-16 | 华南理工大学 | A kind of nano combined conductive hydrogel of polypyrrole and preparation method thereof |
| CN109894102A (en) * | 2019-03-27 | 2019-06-18 | 上海应用技术大学 | The preparation of dopamine/beta-cyclodextrin/reduced graphene gel adsorption material |
| KR20200038374A (en) * | 2018-10-02 | 2020-04-13 | 연세대학교 산학협력단 | Micro-patterned conductive hydrogel hybrid system scaffold and preparing method thereof |
-
2020
- 2020-05-07 CN CN202010379799.5A patent/CN111821516B/en active Active
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2014121378A1 (en) * | 2013-02-05 | 2014-08-14 | University Health Network | Conductive biomaterial for enhancement of conduction in vitro and in vivo |
| CN105906821A (en) * | 2016-04-26 | 2016-08-31 | 西南交通大学 | Preparation method of self-adhesion electroconductive hydrogel |
| CN108467498A (en) * | 2018-06-12 | 2018-08-31 | 华中科技大学 | A kind of supramolecular hydrogel and the preparation method and application thereof of chitosan and gelatin |
| KR20200038374A (en) * | 2018-10-02 | 2020-04-13 | 연세대학교 산학협력단 | Micro-patterned conductive hydrogel hybrid system scaffold and preparing method thereof |
| CN109456444A (en) * | 2018-10-22 | 2019-03-12 | 西南交通大学 | A kind of preparation method for sticking conductive hydrogel for tissue repair |
| CN109575318A (en) * | 2018-11-16 | 2019-04-05 | 华南理工大学 | A kind of polypyrrole conductive hydrogel of DA Mediated and preparation method thereof |
| CN109627461A (en) * | 2018-11-21 | 2019-04-16 | 华南理工大学 | A kind of nano combined conductive hydrogel of polypyrrole and preparation method thereof |
| CN109894102A (en) * | 2019-03-27 | 2019-06-18 | 上海应用技术大学 | The preparation of dopamine/beta-cyclodextrin/reduced graphene gel adsorption material |
Non-Patent Citations (7)
| Title |
|---|
| Catechol modified quaternized chitosan enhanced wet adhesive and antibacterial properties of injectable thermo-sensitive hydrogel for wound healing;Zheng Z等;《Carbohydrate Polymers》;20200803;第249卷;全文 * |
| Coadministration of an Adhesive Conductive Hydrogel Patch and an Injectable Hydrogel to Treat Myocardial Infarction;Wu TL等;《ACS APPLIED MATERIALS & INTERFACES》;20200115;第12卷(第2期);全文 * |
| In situ pPy-modification of chitosan porous membrane from mussel shell as a cardiac patch to repair myocardial infarction;Song X等;《Applied Materials Today》;20190630;第15卷;全文 * |
| Paintable and Rapidly Bondable Conductive Hydrogels as Therapeutic Cardiac Patches;Liang S;《ADVANCED MATERIALS》;20180606;第30卷(第23期);全文 * |
| 林柏仲等.生物黏合水凝胶研究进展.《功能高分子学报》.2020,(第02期), * |
| 生物黏合水凝胶研究进展;林柏仲等;《功能高分子学报》;20200401(第02期);全文 * |
| 聚吡咯导电水凝胶的制备及其生物医学应用研究;胡诗迁;《中国优秀硕士学位论文全文数据库 (医药卫生科技辑)》;20200115(第1期);全文 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN111821516A (en) | 2020-10-27 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN111821516B (en) | Adhesive conductive hydrogel and preparation method and application thereof | |
| Dong et al. | Conductive biomaterials for muscle tissue engineering | |
| Wu et al. | Cell-laden electroconductive hydrogel simulating nerve matrix to deliver electrical cues and promote neurogenesis | |
| Mo et al. | Advances in Injectable and Self‐healing Polysaccharide Hydrogel Based on the Schiff Base Reaction | |
| Vandghanooni et al. | Electrically conductive biomaterials based on natural polysaccharides: Challenges and applications in tissue engineering | |
| Nelson et al. | Intra-myocardial biomaterial injection therapy in the treatment of heart failure: Materials, outcomes and challenges | |
| Zhang et al. | An injectable conductive hydrogel restores electrical transmission at myocardial infarct site to preserve cardiac function and enhance repair | |
| Martins et al. | Electrically conductive chitosan/carbon scaffolds for cardiac tissue engineering | |
| Yeo et al. | Photocrosslinkable hydrogel for myocyte cell culture and injection | |
| Kuzmenko et al. | In situ forming spruce xylan-based hydrogel for cell immobilization | |
| Pal et al. | Therapeutic neovascularization promoted by injectable hydrogels | |
| Tan et al. | Development of alginate-based hydrogels: Crosslinking strategies and biomedical applications | |
| Song et al. | Silk‐based biomaterials for cardiac tissue engineering | |
| Si et al. | Human mesenchymal stem cells encapsulated-coacervated photoluminescent nanodots layered bioactive chitosan/collagen hydrogel matrices to indorse cardiac healing after acute myocardial infarction | |
| CN106492284B (en) | A kind of preparation method of biodegradable filler and products thereof and application | |
| Yan et al. | Advances in the application of supramolecular hydrogels for stem cell delivery and cartilage tissue engineering | |
| CN105233325A (en) | Thermosensitive dual-administration nanocomposite hydrogel as well as preparation method and application thereof | |
| CN111962210B (en) | Polycaprolactone/methacryloylated elastin nanofiber composite membrane and preparation method and application thereof | |
| Arnal-Pastor et al. | Chapter Biomaterials for Cardiac Tissue Engineering | |
| CN105617459A (en) | Preparation method for nano polypyrrole chitin nerve conduit | |
| CN113150561B (en) | Collagen-based biological ink for 3D biological printing and preparation method and application thereof | |
| Zhao et al. | Biomimetic, highly elastic conductive and hemostatic gelatin/rGO-based nanocomposite cryogel to improve 3D myogenic differentiation and guide in vivo skeletal muscle regeneration | |
| CN111888524A (en) | Tissue filling material, preparation method thereof, tissue engineering scaffold and application | |
| CN111905152A (en) | Silicon-based bioactive glass composite hydrogel with self-healing characteristic, preparation method thereof and application thereof in myocardial repair | |
| Hu et al. | A Self-Association Cross-Linked conductive zwitterionic hydrogel as a myocardial patch for restoring cardiac function |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |