WO2021164626A1 - 一种功能化生物基质材料及其制备方法和应用 - Google Patents

一种功能化生物基质材料及其制备方法和应用 Download PDF

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WO2021164626A1
WO2021164626A1 PCT/CN2021/076114 CN2021076114W WO2021164626A1 WO 2021164626 A1 WO2021164626 A1 WO 2021164626A1 CN 2021076114 W CN2021076114 W CN 2021076114W WO 2021164626 A1 WO2021164626 A1 WO 2021164626A1
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solution
biological
matrix material
soak
material according
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PCT/CN2021/076114
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English (en)
French (fr)
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王云兵
雷洋
金林赫
郭高阳
杨立
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杭州启明医疗器械股份有限公司
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Priority claimed from CN202010097281.2A external-priority patent/CN111166938B/zh
Priority claimed from CN202010096214.9A external-priority patent/CN111184914B/zh
Application filed by 杭州启明医疗器械股份有限公司 filed Critical 杭州启明医疗器械股份有限公司
Priority to EP21756791.6A priority Critical patent/EP4108265A4/en
Priority to US17/800,286 priority patent/US20230077632A1/en
Priority to CN202180014565.3A priority patent/CN115087470A/zh
Publication of WO2021164626A1 publication Critical patent/WO2021164626A1/zh

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    • 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
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/3604—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix characterised by the human or animal origin of the biological material, e.g. hair, fascia, fish scales, silk, shellac, pericardium, pleura, renal tissue, amniotic membrane, parenchymal tissue, fetal tissue, muscle tissue, fat tissue, enamel
    • A61L27/3625—Vascular tissue, e.g. heart valves
    • 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
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/3641—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix characterised by the site of application in the body
    • A61L27/367—Muscle tissue, e.g. sphincter
    • 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
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/3683—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix subjected to a specific treatment prior to implantation, e.g. decellularising, demineralising, grinding, cellular disruption/non-collagenous protein removal, anti-calcification, crosslinking, supercritical fluid extraction, enzyme treatment
    • 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
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/3683—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix subjected to a specific treatment prior to implantation, e.g. decellularising, demineralising, grinding, cellular disruption/non-collagenous protein removal, anti-calcification, crosslinking, supercritical fluid extraction, enzyme treatment
    • A61L27/3687—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix subjected to a specific treatment prior to implantation, e.g. decellularising, demineralising, grinding, cellular disruption/non-collagenous protein removal, anti-calcification, crosslinking, supercritical fluid extraction, enzyme treatment characterised by the use of chemical agents in the treatment, e.g. specific enzymes, detergents, capping agents, crosslinkers, anticalcification 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
    • 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
    • A61L27/507—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials for artificial blood vessels
    • 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
    • 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
    • A61L2430/40—Preparation and treatment of biological tissue for implantation, e.g. decellularisation, cross-linking
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N2533/00—Supports or coatings for cell culture, characterised by material
    • C12N2533/90—Substrates of biological origin, e.g. extracellular matrix, decellularised tissue
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N2537/00—Supports and/or coatings for cell culture characterised by physical or chemical treatment
    • C12N2537/10—Cross-linking

Definitions

  • This application relates to the technical field of medical materials, in particular to a functionalized biological matrix material and its preparation method and application.
  • biological heart valves in commercial applications are generally made of bovine pericardium, porcine heart valve and porcine pericardium through glutaraldehyde cross-linking.
  • the glutaraldehyde cross-linking method is simple in process, low in cost, and collagenous.
  • the structure is stable and good mechanical properties, but the glutaraldehyde cross-linked heart valve has problems that cannot be ignored.
  • the glutaraldehyde cross-linking cannot protect the elastin, which will easily cause the mechanical properties of the heart valve to decrease; Aldehyde cross-linked heart valves are prone to residual and calcification problems, which will affect their service life (only 10 years); glutaraldehyde and residual aldehyde groups are highly toxic, easily triggering inflammatory reactions and causing valve failure.
  • glutaraldehyde cross-linked biological heart valves many methods have been used to improve or replace glutaraldehyde cross-linking. For example, after glutaraldehyde is cross-linked, it is treated with reagents such as bisphosphonates, ⁇ -aminooleic acid and ethanol to block the aldehyde group, but the effect is not significant.
  • some new cross-linking methods have also been tried for the cross-linking of biological heart valves, such as carbodiimide, polyepoxy compounds and genipin.
  • Carbodiimide mainly promotes nucleophilic substitution of amino groups in eggs. It reacts with carboxyl groups to form amide bonds to cross-link collagen.
  • the currently used transcatheter biological valve products generally need to be immersed in glutaraldehyde solution for long-term storage.
  • the residual glutaraldehyde needs to be cleaned temporarily before surgery, and then installed into the valve delivery system at the operation site by pressing and holding it.
  • the problem of glutaraldehyde residue has also led to the cumbersome preoperative preparation process and increased risk of surgical accessories.
  • this application provides a functionalized biological matrix material and its preparation method and application, which can replace the traditional cross-linking method of glutaraldehyde, and at the same time introduce 3-sulfonic acid propyl methacrylate to give biological
  • the matrix material has better biocompatibility.
  • a preparation method of functionalized biological matrix material includes the following steps:
  • the biological matrix material After cleaning the biological matrix material, it is immersed in glycidyl methacrylate or methacrylic anhydride aqueous solution, and then immersed in the 3-sulfonic acid propyl methacrylate aqueous solution, and then an initiator is added to initiate the polymerization reaction. Realize the cross-linking and functional processing of biological matrix materials.
  • 3-sulfonic acid propyl methacrylate can form a polymer network in the collagen network of the biological matrix material .
  • the sulfonic acid group can improve the hydrophilicity, so that the dry film can quickly absorb water and recover in the human environment after it is released.
  • the steps of preparing the biological matrix material have a specific sequence of operations and synergistic internal factors.
  • the biological matrix material is soaked in glycidyl methacrylate or methacrylic anhydride aqueous solution to introduce a carbon-carbon double bond structure, and then soaked in In the aqueous solution of 3-sulfonic acid propyl methacrylate, the 3-sulfonic acid propyl methacrylate is distributed between the protein fibers of the biological matrix material by physical penetration, and finally, an initiator is added for double bond polymerization and cross-linking .
  • the biological matrix material of this application does not strictly require decellularization before the modification treatment, which can avoid damage to the mechanical properties; of course, in some schemes, the biological matrix material can also be pre-decellularized, mainly for cleaning animals.
  • the cells remaining in the tissue due to the cutting and peeling method further reduce the immunogenicity of the heterogeneous implant material.
  • the biological matrix material is decellularized animal tissue, the animal tissue is derived from pigs, cattle or sheep; the animal tissue includes blood vessels, heart valves and pericardium, and its main components are collagen, At least one of elastin and glycosaminoglycan.
  • the cleaning solution can be water, ethanol, Acetone and so on.
  • the concentration of the methacrylic anhydride aqueous solution is 1-20 wt%, preferably 1-5 wt%.
  • the cleaned biological matrix material is immersed in an aqueous solution of methacrylic anhydride and reacted for 6-72h at 4-60°C.
  • it is immersed in a methacrylic anhydride aqueous solution at 20-40° C. and reacted for 18-24 hours.
  • the cleaned biological matrix material reacts with methacrylic anhydride, and the amino group in the biological matrix material reacts with methacrylic anhydride to form an amide bond. Due to the low concentration, low temperature and short time of methacrylic anhydride solution, the reaction between the bio-based material and methacrylic anhydride will be incomplete, and the density of cross-linking points will decrease, so that the bio-based material cannot be fully cross-linked, which affects the use of bio-based materials. performance. Excessive temperature will cause damage to the structure of the biological matrix material. However, the high concentration and long time of methacrylic anhydride will cause unnecessary cost waste.
  • concentration of the 3-sulfonic acid propyl methacrylate aqueous solution is 10-500 mmol/L.
  • the initiator is a photoinitiator or a thermal initiator; the photoinitiator is at least one of potassium persulfate, sodium persulfate and ammonium persulfate, and the thermal initiator is 2-hydroxy-2 -Methyl-1-phenylacetone, 1-hydroxycyclohexylphenyl ketone, 2-methyl-2-(4-morpholinyl)-1-[4-(methylthio)phenyl]-1 -Acetone, 2-hydroxy-4'-(2-hydroxyethoxy)-2-methylpropiophenone, 2,4,6-trimethylbenzoyl-diphenylphosphine oxide and 2-hydroxy-2 -At least one of methyl-1-[4-(2-hydroxyethoxy)phenyl]-1-acetone.
  • the reaction conditions are polymerization reaction at 20-45° C. for 18-48 hours; when the photoinitiator is used, the reaction conditions are reaction at room temperature under an ultraviolet light source for 5-30 minutes.
  • the polymerization reaction is free polymerization, in which the monomer concentration, reaction time, and reaction temperature should be within the specified range so that the polymerization reaction can occur, and the degree of polymerization is large enough to increase the cross-linking density and increase the stability of the biological matrix material structure. Below the specified range, the reaction will be incomplete, the concentration of the inserted monomer will be too low, and the effect of improving the function will be reduced. The high reaction temperature will destroy the structure of the biological matrix material. Too high monomer concentration and reaction time will lead to cost waste.
  • the preparation method further includes the following steps after initiating the polymerization reaction:
  • the material obtained by cross-linking and fixing is immersed in a polyphenol solution.
  • the material after immersion treatment in the polyphenol solution is rinsed and stored in a bacteriostatic solvent or stored after dehydration and drying in an alcohol solution.
  • the alcohol solution is a mixed solution of glycerol and ethanol or a mixed solution of glycerol, ethanol and isopropanol.
  • the alcohol solution is a mixed solution of 10-30vt% glycerol and 70-90vt% ethanol or a mixed solution of 10-30vt% glycerol, 35-45vt% ethanol and 35-45vt% isopropanol.
  • the double bond polymerization reaction is thermally initiated at 20-45° C. for 12-48 h; wherein the initiator is at least one of potassium persulfate, ammonium persulfate, sodium bisulfite and tetramethylethylenediamine.
  • the specific steps of immersing the material obtained by cross-linking and fixing in the polyphenol solution include:
  • polyphenols are curcumin, proanthocyanidins, quercetin, resveratrol, aloin, aloe-emodin, tannin At least one of acid, epigallocatechin gallate, pentagallocatechin and genipin.
  • This application also provides functionalized biological matrix materials prepared by any of the above-mentioned methods.
  • the application also provides the application of the functionalized biological matrix material in the preparation of medical materials.
  • the medical materials are thoracotomy biological valves, interventional biological valves, tissue-engineered valves, biological patches, artificial blood vessels or tissue-engineered blood vessels.
  • the functionalized biological matrix material has the following advantages:
  • the present invention realizes multi-site, long-range cross-linking of biological matrix materials through polymer network, and at the same time introduces corresponding functional functional groups to realize the functionalization of biological matrix materials; even if methacrylic anhydride and biological matrix materials are The amino residues reacted fully, modified allyl, methallyl and other carbon-carbon double bond structures in the biological matrix material, and then soaked in an aqueous solution containing 3-sulfonic acid propyl methacrylate to give it a better biological Compatibility, and finally cross-link and functionalize the biological matrix material by free radical polymerization; the present invention improves the hydrophilicity of the material by introducing functional monomers with anticoagulant effect, and effectively reduces the adhesion of platelets. Attached, the anticoagulant performance of the biological matrix material is improved; the method of the present invention can enable the material to have different functions by introducing different substances;
  • the method of the present invention forms an interpenetrating network with the polymer to increase the cross-linking density and protect the elastin, improve the stability of the elastin, and improve the mechanical properties of the biological matrix material, thereby prolonging the service life of the material;
  • the present application also provides a method for preparing non-glutaraldehyde by using the functionalized biological matrix material. The method and application of pre-installed dry biological valve material.
  • This application also provides a method for preparing a non-glutaraldehyde preloadable dry biological valve material, which includes the following steps:
  • step b Soak the material treated in step b in an aqueous solution of 3-propyl methacrylate sulfonate;
  • step d Add an initiator to the material processed in step c for double bond polymerization and crosslinking;
  • step d Use a mixed solution of carbodiimide and N-hydroxysuccinimide to cross-link and fix the material obtained in step d;
  • step e Soak the material obtained in step e in a polyphenol solution
  • step f Rinse the material treated in step f, store it in a bacteriostatic solvent or store it after dehydration and drying in an alcohol solution, and get it.
  • Carbodiimide mainly promotes the cross-linking of collagen by nucleophilic substitution of amino groups and carboxyl groups in egg deterioration to form amide bonds, but the resulting chemical bonds are easily hydrolyzed and the cross-linking stability is poor. Therefore, polyphenol cross-linking was added later.
  • the pericardial material treated with polyphenolic cross-linking agent further enhanced the cross-linking strength and component stability of the pericardial material through hydrogen bonding. After transplantation, no calcification occurred, and the mechanical strength was comparable to that of glutaric acid.
  • the aldehyde is equivalent, and further cross-linking overcomes the instability of carbodiimide cross-linking and improves the stability of the product.
  • the biological valve material utilizes all reactive groups to increase the degree of cross-linking as much as possible to meet the needs of use.
  • Step a to step d are essentially the same operations as the above-mentioned functionalized biological matrix material preparation method.
  • the functionalized biological matrix material can also adopt the operations of step e to step g to further obtain a dry biological valve that can be pre-installed Material.
  • the step a includes decellularizing the animal pericardium material.
  • the biological valve material provided in this application is a dry membrane, which can be directly pre-squeezed and loaded into the device, and is always in a compressed state before use. In order to quickly flatten after being released in the patient's body, avoid excessive folds. It is necessary to improve the stability of elastin through multi-step combined cross-linking (the amino content of elastin is low, and the carboxyl, hydroxyl and other groups can fully participate in cross-linking through combined cross-linking, thereby improving the stability of elastin). In addition, in step c Introduced methacrylic acid-3-sulfonic acid propyl ester to further improve the hydrophilicity, so that the dry film can quickly absorb water in the human environment to restore and flatten.
  • step b the biological matrix material is immersed in the aqueous solution of glycidyl methacrylate or methacrylic anhydride in order to introduce a carbon-carbon double bond structure.
  • the methacrylic acid-3-sulfonic acid propyl ester is physically infiltrated by soaking, and then initiates polymerization together with the double bond substance introduced in the previous step b.
  • the methacrylic acid-3-sulfonic acid propyl ester is not used in isolation. It uses the double bond structure and the double bond introduced in step b to interact with each other.
  • the substances used in step b and step c need to have CC double bonds, so in step d
  • the double bond-initiated polymerization can only be carried out at one time, and step b should be implemented before step c. Otherwise, if step c is performed first, the sulfonic acid group soaking effect is not good, and protein fibers will be washed out in the subsequent processing steps.
  • the animal pericardium material is taken from pigs, cattle or sheep.
  • the decellularization in step a specifically includes: soaking the pericardium in a 0.01-1wt% disodium edetate solution for 1-4h, and then in 0.01-1wt% sodium lauryl sulfate Soak in the solution for 1-24h, then rinse in sterile PBS solution for 1-24h.
  • the pericardium is soaked in 0.05-0.3wt% disodium ethylenediaminetetraacetic acid solution for 1-2h, and then immersed in 0.05-0.3wt% sodium lauryl sulfate solution for 12-24h, then Rinse in sterile PBS solution for 1-10h.
  • step b is specifically: immersing the decellularized pericardium in a 1-10 wt% glycidyl methacrylate solution at 25-45°C for 3-7 d, or 1-5 wt% Soak in methacrylic anhydride aqueous solution for 12-48h.
  • step c is specifically: immersing the material in a 0.01-1M 3-sulfonic acid propyl methacrylate aqueous solution at 25-45° C. for 12-48 h.
  • the material is immersed in a 0.05-0.5M 3-sulfonic acid propyl methacrylate aqueous solution at 30-40°C for 12-48h.
  • step d is specifically: thermally initiating the double bond polymerization reaction at 20-45° C. for 12-48 h; wherein the initiator is potassium persulfate, ammonium persulfate, sodium bisulfite and tetramethyl ethyl At least one of diamines.
  • the step e is specifically: the material after the double bond polymerization and cross-linking treatment at 25-45 °C in water of 10-60 mM carbodiimide and 1-20 mM N-hydroxysuccinimide Soak in the mixed pH buffer solution for 24-48h.
  • the step f specifically includes: immersing the cross-linked and fixed material in a 0.01-10 mM polyphenolic compound aqueous solution for 1-24 h; wherein the polyphenolic compound is curcumin, proanthocyanidin, quercetin, and quinoa At least one of atlol, aloin, aloe-emodin, tannic acid, epigallocatechin gallate, pentagalloyl glucose, and genipin.
  • the bacteriostatic solvent storage is specifically: immersing the prepared biological valve material in 20-100vt% isopropanol or 70-100vt% ethanol aqueous solution for storage; the alcohol solution is dehydrated and dried and stored specifically as follows: The prepared biological valve material is immersed in a mixed solution of 10-30vt% glycerol and 70-90vt% ethanol or a mixed solution of 10-30vt% glycerol, 35-45vt% ethanol and 35-45vt% isopropanol for 4-24h, and dried, That's it.
  • the non-glutaraldehyde prepared by any of the above methods can be pre-filled with dry biological valve material.
  • the biological valves including artificial aortic valves, pulmonary valves, venous valves, mitral valves and tricuspid valves.
  • the present invention adopts acrylic acid-based shrinkage
  • the pericardium modified by glycerides or methacrylic anhydride is polymerized and cross-linked by double bond, carbodiimide and polyphenol compounds are composite cross-linked, and the biological valve is developed into a dry interventional biological valve preserved from glutaraldehyde solution, and Pre-loaded in the valve delivery system, compared with glutaraldehyde cross-linked pericardium, it has better anti-calcification performance and elastin stability, as well as the rapid flattening performance of the dried valve material after compression, which solves the existing problem.
  • the short lifespan of biological valves due to easy calcification and the inability to protect elastin can prolong their lifespan, which is of great significance for the scientific research
  • Figure 1 is a graph of the weight loss rate of elastase degradation
  • Figure 2 is a diagram of calcium content
  • Figure 3 is a graph of relative endothelial cell adhesion rate
  • Figure 4 shows the result of the water immersion flattening test.
  • first and “second” and other relational terms are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply one of these entities or operations. There is any such actual relationship or order between.
  • the terms “include”, “include” or any other variants thereof are intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements not only includes those elements, but also includes those that are not explicitly listed Other elements of, or also include elements inherent to this process, method, article or equipment. If there are no more restrictions, the element defined by the sentence “including a" does not exclude the existence of other same elements in the process, method, article, or equipment that includes the element.
  • a method for preparing a functionalized biological matrix material provided by a preferred embodiment of the present invention, the specific steps are as follows:
  • a method for preparing a functionalized biological matrix material provided by a preferred embodiment of the present invention, the specific steps are as follows:
  • a method for preparing a functionalized biological matrix material provided by a preferred embodiment of the present invention, the specific steps are as follows:
  • a method for preparing a functionalized biological matrix material provided by a preferred embodiment of the present invention, the specific steps are as follows:
  • a method for preparing a functionalized biological matrix material provided by a preferred embodiment of the present invention, the specific steps are as follows:
  • a method for preparing a functionalized matrix biomaterial provided by a preferred embodiment of the present invention, the specific steps are as follows:
  • the material is ultrasonically cleaned with distilled water to get it.
  • glutaraldehyde flap Using traditional glutaraldehyde cross-linking to prepare acellular matrix biomaterials to prepare samples, referred to as glutaraldehyde flap: soak the porcine pericardium in a 0.1wt% disodium ethylenediaminetetraacetic acid solution for 1h, and then soak in 0.1wt% Sodium lauryl sulfate solution for 24h, then rinsed in sterile PBS solution for 1h, and then immersed in 0.1vt%, 0.5vt%, 1vt% glutaraldehyde PBS solution for crosslinking for 24h.
  • hybrid flaps They are the materials prepared in Examples 1-3, referred to as hybrid flaps.
  • acellular matrix biological material abbreviated as acellular flap.
  • Example 1 can effectively protect the elastin in the acellular matrix, potentially improving its mechanical properties and prolonging its service life. This is because the biomaterial prepared according to the method of the present invention increases the crosslink density by forming an interpenetrating network with the polymer, thereby protecting elastin.
  • the method of the present invention can effectively reduce the calcification reaction. This is because the acellular matrix biomaterial prepared according to the method of the present invention does not incorporate Glutaraldehyde, while shielding most of the residues in the acellular matrix, reduces the ability of the acellular matrix material to bind calcium ions, thereby reducing the calcification reaction.
  • the method of the present invention can effectively improve the adsorption of endothelial cells on the acellular matrix biological material.
  • the acellular matrix biomaterial prepared according to the method of the present invention does not introduce glutaraldehyde, a biotoxic crosslinking agent, instead of a biocompatible crosslinking agent, and at the same time, it introduces a crosslinking agent that promotes endothelium
  • the functional monomer for cell growth and migration further improves the biocompatibility.
  • a preferred embodiment of the present invention provides a method for preparing a non-glutaraldehyde preloadable dry biological valve material, and the specific steps are as follows:
  • a preferred embodiment of the present invention provides a method for preparing a non-glutaraldehyde preloadable dry biological valve material, and the specific steps are as follows:
  • a preferred embodiment of the present invention provides a method for preparing a non-glutaraldehyde preloadable dry biological valve material, and the specific steps are as follows:
  • a preferred embodiment of the present invention provides a method for preparing a non-glutaraldehyde preloadable dry biological valve material, and the specific steps are as follows:
  • a preferred embodiment of the present invention provides a method for preparing a non-glutaraldehyde preloadable dry biological valve material, and the specific steps are as follows:
  • control group and the materials prepared in Examples 7, 8 and Comparative Examples 1-4 were respectively subjected to the anti-calcification performance test, the elastin stability test and the water immersion flattening test.
  • Control group the porcine pericardium was soaked in a 0.1wt% disodium ethylenediaminetetraacetic acid solution for 1h, then soaked in a 0.1wt% sodium lauryl sulfate solution for 24h, and then rinsed in a sterile PBS solution For 1h, soak in 0.1vt%, 0.5vt%, 1vt% glutaraldehyde PBS solution for crosslinking for 24h, then soak in 20vt% glycerol, 40vt% ethanol and 40vt% isopropanol mixed solution for 4h, and air dry Store at room temperature afterwards.
  • One sample of the test group was implanted subcutaneously on the right back, and one sample of the control group was implanted subcutaneously on the left back, and the skin incision was sutured. After 60 days, the animals were euthanized by cervical dislocation and the grafts were taken out.
  • the anti-calcification performance tests were performed on the materials prepared in the examples and the control, and the results are shown in Table 1 below. It can be seen from Table 1 that the calcium content of the materials prepared in Example 7 and Example 8 is greatly reduced compared to the control group, and the calcium content of the materials prepared in Example 7 and Example 8 is less than that of Comparative Examples 1-4, so , The material of the present invention has excellent anti-calcification performance.
  • In vitro enzyme degradation test is an effective method to test the ability of biological valves to resist protease degradation.
  • elastase 30 U/mL
  • the materials prepared in Examples 7, 8, Comparative Examples 1-4, and the control group were subjected to fold and pressure immersion test respectively.
  • the specific test is as follows: a plastic tube with an inner diameter of 5 mm is used for a simulated fold and pressure test, and the area of each group of materials is cut with scissors For a square sample with a size of about 3cm*3cm, use tweezers to slowly insert the square sample into a plastic tube with an inner diameter of 5mm, and then place it in a constant temperature and humidity box with a temperature of 40°C and a humidity of 60%-80% for 72 hours. The material is extruded out of the plastic tube and immersed in PBS buffer, observe and take pictures to record the water immersion and flattening.
  • the water immersion flattening is shown in FIG. 4, the water immersion flattening conditions of the example and the comparison group are better, while the (glutaraldehyde) control group cannot flatten quickly, and the creases are more obvious.

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Abstract

本申请公开了一种功能化生物基质材料及其制备方法和应用，属于医用材料技术领域。本发明通过将生物基质材料与甲基丙烯酸3-磺酸丙酯杂化，同时实现了对生物基质材料的交联及功能化。具体方法包括在生物基质材料中修饰烯丙基、甲基烯丙基等碳碳双键结构，再将生物基质材料浸泡在含有甲基丙烯酸3-磺酸丙酯水溶液中，最后通过自由基聚合的方式对生物基质材料进行交联及功能化，利用该生物基质材料制作瓣膜等材料。本发明通过聚合物网络实现对生物基质材料的多位点、长程交联，同时引入了相应的功能性官能团从而实现对生物基质材料的功能化。

Description

一种功能化生物基质材料及其制备方法和应用 技术领域
本申请涉及医用材料技术领域，特别是涉及一种功能化生物基质材料及其制备方法和应用。
 背景技术
目前商业应用的生物心脏瓣膜一般是由牛心包膜、猪心瓣膜和猪心包膜通过戊二醛交联制备而成，戊二醛交联的方法据有工艺简单、成本低廉、胶原蛋白结构稳定及较好的力学性能，但戊二醛交联的心脏瓣膜存在不容忽视的问题，由戊二醛交联不能对弹性蛋白起到保护作用，容易引起心脏瓣膜的力学性能下降；戊二醛交联的心脏瓣膜容易发生残留以及钙化问题，影响使用寿命（只有10年）；戊二醛及残余的醛基具有较强毒性，易引发炎症反应，造成瓣膜失效。
为了克服戊二醛交联的生物心脏瓣膜的缺点，很多方法被用于改进或代替戊二醛交联。例如在戊二醛交联后使用二磷酸盐类、α-氨基油酸和乙醇等试剂进行处理，封闭醛基，但是效果并不显著。此外，一些新的交联方法也被尝试用于生物心脏瓣膜的交联，如碳化二亚胺、多环氧化合物和京尼平，碳化二亚胺主要通过亲核取代促使蛋变质中的氨基与羧基反应形成酰胺键对胶原蛋白进行交联，这种方法没有引入有毒的醛基，但由于只能交联邻近的氨基和羧基，所以交联的效果较差。多环氧化合物通过环氧基与氨基、羧基、羟基等基团反应，从而将蛋白质交联起来，但由于生成的化学键容易水解，因此交联稳定性欠佳。京尼平的毒性比戊二醛小，但京尼平交联的生物心脏瓣膜长期稳定性和机械性能不如戊二醛交联方法，同时京尼平处理后生物瓣膜变为蓝色，因此，京尼平也没有被广泛的应用。
其次，当前使用的经导管生物瓣膜产品一般需要浸泡于戊二醛溶液中长期保存，术前需要临时清洗残留的戊二醛，再通过压握，手术现场安装至瓣膜输送系统中，这既带来了戊二醛残留的问题，同时导致术前准备流程繁琐，手术附件风险增大。
 技术问题
针对现有技术中存在的不足，本申请提供一种功能化生物基质材料及其制备方法和应用，能够替代传统戊二醛的交联方式，同时引入甲基丙烯酸3-磺酸丙酯赋予生物基质材料更好的生物相容性。
 技术解决方案
一种功能化生物基质材料的制备方法，包括以下步骤：
将生物基质材料清洗后，浸泡在甲基丙烯酸缩水甘油酯或甲基丙烯酸酐水溶液中，然后再浸泡在甲基丙烯酸3-磺酸丙酯水溶液中，之后加入引发剂引发聚合反应。实现对生物基质材料的交联和功能化处理。
本申请在生物基质材料中引入含有磺酸基以及不饱和双键官能团的双官能团两亲性分子甲基丙烯酸3-磺酸丙酯后，其能够在生物基质材料的胶原网络中形成聚合物网络，赋予生物基质材料更好的生物相容性，更重要的是磺酸基可改善亲水性，使干膜释放后在人体环境内快速吸水复原展平。
制备生物基质材料的各步骤之间具有特定的操作次序和协同内因，将生物基质材料浸泡在甲基丙烯酸缩水甘油酯或甲基丙烯酸酐水溶液中，是为了引入碳碳双键结构，然后浸泡在甲基丙烯酸3-磺酸丙酯水溶液中，通过物理渗透的方式使甲基丙烯酸3-磺酸丙酯分布于生物基质材料的各蛋白纤维之间，最后，加入引发剂进行双键聚合交联。
以下还提供了若干可选方式，但并不作为对上述总体方案的额外限定，仅仅是进一步的增补或优选，在没有技术或逻辑矛盾的前提下，各可选方式可单独针对上述总体方案进行组合，还可以是多个可选方式之间进行组合。
本申请生物基质材料在实施改性处理之前并不严格要求需要脱细胞处理，这样可避免力学性能受损；当然在一些方案中也可对生物基质材料预先进行脱细胞处理，主要用于清理动物组织上因切割的剥离方式残留的细胞，进一步降低异种植入材料的免疫原性。
进一步地，所述生物基质材料为经过脱细胞处理的动物组织，所述动物组织来源于猪、牛或羊；所述动物组织包括血管、心脏瓣膜和心包膜，其主要成分为胶原蛋白、弹性蛋白和糖胺多糖中的至少一种。
在动物组织中加入脱细胞试剂进行脱细胞处理，确保细胞脱除干净，然后使用清洗液对生物基质材料进行清洗，将残留的细胞、脱细胞试剂等杂质去除；清洗液可采用水、乙醇、丙酮等。
进一步地，所述甲基丙烯酸酐水溶液的浓度为1-20wt%，优选为1-5wt%。
进一步地，所述清洗后的生物基质材料在4-60℃下浸泡在甲基丙烯酸酐水溶液中反应6-72h。优选为在20-40℃下浸泡在甲基丙烯酸酐水溶液中反应18-24h。
清洗后的生物基质材料与甲基丙烯酸酐反应，通过生物基质材料中氨基与甲基丙烯酸酐反应生成酰胺键键合。由于甲基丙烯酸酐溶液浓度低、温度低、时间短会导致生物基质材料与甲基丙烯酸酐反应不完全，交联点密度下降，使生物基质材料不能被充分交联，影响生物基质材料的使用性能。温度过高会导致生物基质材料结构遭到破坏。而甲基丙烯酸酐浓度高、时间长会造成不必要的成本浪费。因此需在本发明所采用的温度、时间以及甲基丙烯酸酐溶液浓度下，将生物基质材料与甲基丙烯酸酐水溶液震荡充分接触，使甲基丙烯酸酐与生物基质材料中的氨基残基充分反应，提高接入双键的含量，提高交联密度，进而使交联生物基质材料更加稳定。
进一步地，所述甲基丙烯酸3-磺酸丙酯水溶液浓度为10-500mmol/L。
进一步地，在4-60℃下于甲基丙烯酸3-磺酸丙酯水溶液中浸泡2-72h，优选为在20-45℃下于甲基丙烯酸3-磺酸丙酯水溶液中浸泡18-36h。
在浸泡在甲基丙烯酸3-磺酸丙酯水溶液之前，采用乙醇和水等体积混合的清洗剂进行清洗，将未反应的游离甲基丙烯酸酐清洗干净。在浸泡时，将生物基质材料与甲基丙烯酸3-磺酸丙酯水溶液震荡充分接触，确保甲基丙烯酸3-磺酸丙酯均匀分散。
进一步地，所述引发剂为光引发剂或热引发剂；所述光引发剂为过硫酸钾、过硫酸钠和过硫酸铵中的至少一种，所述热引发剂为2-羟基-2-甲基-1-苯基丙酮、1-羟基环己基苯基甲酮、2-甲基-2-(4-吗啉基)-1-[4-(甲硫基)苯基]-1-丙酮、2-羟基-4'-(2-羟乙氧基)-2-甲基苯丙酮、2,4,6-三甲基苯甲酰基-二苯基氧化膦和2-羟基-2-甲基-1-[4-(2-羟基乙氧基)苯基]-1-丙酮中的至少一种。
进一步地，采用所述热引发剂时反应条件为在20-45℃下聚合反应18-48h；采用所述光引发剂时反应条件为在紫外光源下于室温中反应5-30min。
聚合反应为自由聚合，其中单体浓度、反应时间、反应温度应在指定范围内，使聚合反应可以发生，聚合度足够大以提高交联密度，增加生物基质材料结构的稳定性。低于指定范围会导致反应不完全，接入单体浓度过低，改善功能效果下降。而反应温度过高会破坏生物基质材料结构。单体浓度、反应时间过高会导致成本浪费。
进一步地，所述制备方法还包括在引发聚合反应后，进行以下步骤：
采用碳二亚胺和N-羟基丁二酰亚胺混合溶液对聚合反应后所得材料进行交联固定；
将交联固定所得材料浸泡于多酚溶液中。
进一步地，将经多酚溶液浸泡处理后的材料漂洗，采用抑菌溶剂保存或采用醇溶液脱水干燥后保存。
进一步地，所述醇溶液为甘油与乙醇混合溶液或甘油、乙醇与异丙醇的混合溶液。
进一步地，所述醇溶液为10-30vt%甘油与70-90vt%乙醇混合溶液或10-30vt%甘油、35-45vt%乙醇与35-45vt%异丙醇混合溶液。
进一步地，所述加入引发剂引发聚合反应，具体步骤包括：
在20-45℃的条件下热引发双键聚合反应12-48h；其中，引发剂为过硫酸钾、过硫酸铵、亚硫酸氢钠和四甲基乙二胺中的至少一种。
进一步地，将交联固定所得材料浸泡于多酚溶液中具体步骤包括：
将交联固定后材料于0.01-10 mM多酚类化合物水溶液中浸泡1-24h；多酚类化合物为姜黄素、原花青素、槲皮素、白藜芦醇、芦荟素、芦荟大黄素、单宁酸、表没食子儿茶素没食子酸酯、五没食子酰葡萄糖和京尼平中的至少一种。
本申请还提供采用上述任一方法制备得到的功能化生物基质材料。
本申请还提供所述功能化生物基质材料在制备医用材料中的应用，所述医用材料为开胸生物瓣膜、介入生物瓣膜、组织工程瓣膜、生物补片、人工血管或组织工程血管。
所述功能化生物基质材料相比现有技术具有以下优点：
1、本发明通过聚合物网络实现对生物基质材料的多位点、长程交联，同时引入了相应的功能性官能团从而实现对生物基质材料的功能化；即使甲基丙烯酸酐与生物基质材料中的氨基残基充分反应，在生物基质材料中修饰烯丙基、甲基烯丙基等碳碳双键结构，再浸泡在含有甲基丙烯酸3-磺酸丙酯水溶液中赋予其更好的生物相容性，最后通过自由基聚合的方式对生物基质材料进行交联及功能化；本发明通过引入具有抗凝血作用的功能性单体，提高了材料的亲水性，有效降低血小板的粘附，提高了生物基质材料的抗凝血性能；采用本发明的方法通过引入不同的物质能够使材料具备不同的功能；
2、本发明方法通过与聚合物形成互穿网络提高交联密度保护弹性蛋白，提高了弹性蛋白的稳定性，提高了生物基质材料材料的力学性能，从而延长了材料的使用寿命；
3、本发明方法由于未引入戊二醛，同时遮蔽了大部分残基，使其与钙离子结合能力下降，因此可以有效降低钙化反应，提高抗钙化性能。
为解决戊二醛醛基残留、容易钙化、无法保护弹性蛋白以及干燥瓣膜材料压握后不能快速展平的问题，本还申请提供一种利用所述功能化生物基质材料制备非戊二醛可预装干燥生物瓣膜材料的方法和应用。
本申请还提供了一种非戊二醛可预装干燥生物瓣膜材料的制备方法，包括以下步骤：
a.获取动物心包膜材料；
b.将心包膜材料浸泡在甲基丙烯酸缩水甘油酯或丙烯酸酐溶液中，以引入碳碳双键结构；
c.将经步骤b处理的材料浸泡在甲基丙烯酸3-磺酸丙酯水溶液中；
d.在经步骤c处理的材料中加入引发剂进行双键聚合交联；
e.采用碳二亚胺和N-羟基丁二酰亚胺混合溶液对步骤d所得材料进行交联固定；
f.将步骤e所得材料浸泡于多酚溶液中；
g.将经步骤f处理的材料漂洗，采用抑菌溶剂保存或采用醇溶液脱水干燥后保存，即得。
碳二亚胺主要通过亲核取代促使蛋变质中的氨基与羧基反应形成酰胺键对胶原蛋白进行交联，但由于生成的化学键容易水解，交联稳定性欠佳。因此之后增加了多酚交联，用多酚类交联剂处理的心包材料通过氢键作用进一步增强心包材料交联强度和组分稳定性，，移植后不发生钙化，且机械强度与戊二醛相当，进一步交联克服了碳二亚胺交联不稳定的缺陷，提高了产品的稳定性。生物瓣膜材料利用所有反应基团尽可能地提高交联度，以满足使用需求。
步骤a~步骤d与前述的功能化生物基质材料的制备方法为本质相同的操作，所述的功能化生物基质材料也可以采用步骤e~步骤g的操作，进一步得到可以预装的干燥生物瓣膜材料。
以下还提供了若干可选方式，但并不作为对上述总体方案的额外限定，仅仅是进一步的增补或优选，在没有技术或逻辑矛盾的前提下，各可选方式可单独针对上述总体方案进行组合，还可以是多个可选方式之间进行组合。
进一步地，所述步骤a包括将动物心包膜材料脱细胞。
本申请提供的生物瓣膜材料为干膜，可直接预先压握装载在器械中，在使用前始终处于压缩状态，为了在患者体内释放后进行快速的展平，避免过多的褶皱残留，一方面需要通过多步骤的组合交联提高弹性蛋白稳定性（弹性蛋白氨基含量低，通过组合交联使羧基、羟基等基团充分参与交联，从而提高弹性蛋白的稳定性）、另外在步骤c中引入了甲基丙烯酸-3-磺酸丙脂，进一步提高了亲水性，以便干膜在人体环境内快速吸水复原展平。制备生物基质材料的各步骤之间具有特定的操作次序和协同内因，步骤b，将生物基质材料浸泡在甲基丙烯酸缩水甘油酯或甲基丙烯酸酐水溶液中，是为了引入碳碳双键结构，甲基丙烯酸-3-磺酸丙脂采用浸泡的方式进行物理渗透，而后与之前步骤b引入的双键物质一并进行引发聚合。
甲基丙烯酸-3-磺酸丙脂也并非孤立使用，其利用双键结构与步骤b引入的双键相互协同反应，步骤b和步骤c所用物质都需要带有C-C双键，这样在步骤d中才可以一次性进行双键引发聚合，步骤b要在步骤c之前实施，否则若先执行步骤c，则磺酸基团浸泡效果不佳，会在后续处理步骤冲洗出蛋白纤维。
进一步地，所述步骤a中动物心包膜材料取自猪、牛或羊。
进一步地，所述步骤a中脱细胞具体为：将心包膜于0.01-1wt%的乙二胺四乙酸二钠溶液中浸泡1-4h，再于0.01-1wt%的十二烷基硫酸钠溶液中浸泡1-24h，然后在无菌PBS溶液中漂洗1-24h。
优选为：将心包膜于0.05-0.3wt%的乙二胺四乙酸二钠溶液中浸泡1-2h，再于0.05-0.3wt%的十二烷基硫酸钠溶液中浸泡12-24h，然后在无菌PBS溶液中漂洗1-10h。
进一步地，所述步骤b具体为：在25-45℃下将脱细胞的心包膜于1-10wt%的甲基丙烯酸缩水甘油酯溶液中浸泡3-7d，或于1-5 wt%的甲基丙烯酸酐水溶液中浸泡12-48h。
进一步地，所述步骤c具体为：在25-45℃下将材料于0.01-1M的甲基丙烯酸3-磺酸丙酯水溶液中浸泡12-48h。
优选为：在30-40℃下将材料于0.05-0.5M的甲基丙烯酸3-磺酸丙酯水溶液中浸泡12-48h。
进一步地，所述步骤d具体为：在20-45℃的条件下热引发双键聚合反应12-48h；其中，引发剂为过硫酸钾、过硫酸铵、亚硫酸氢钠和四甲基乙二胺中的至少一种。
进一步地，所述步骤e具体为：在25-45℃下将双键聚合交联处理后的材料在10-60 mM碳二亚胺和1-20 mM N-羟基丁二酰亚胺的水混合pH缓冲溶液中浸泡24-48h。
进一步地，所述步骤f具体为：将交联固定后材料于0.01-10 mM多酚类化合物水溶液中浸泡1-24h；其中，多酚类化合物为姜黄素、原花青素、槲皮素、白藜芦醇、芦荟素、芦荟大黄素、单宁酸、表没食子儿茶素没食子酸酯、五没食子酰葡萄糖和京尼平中的至少一种。
进一步地，抑菌溶剂保存具体为：将制得的生物瓣膜材料浸泡于20-100vt%的异丙醇或70-100vt%的乙醇水溶液中保存；所述醇溶液脱水干燥后保存具体为：将制得的生物瓣膜材料浸泡于10-30vt%甘油与70-90vt%乙醇混合溶液或10-30vt%甘油、35-45vt%乙醇与35-45vt%异丙醇混合溶液中4-24h，干燥，即可。
上述任一方法制备得到的非戊二醛可预装干燥生物瓣膜材料。
上述非戊二醛可预装干燥生物瓣膜材料在制备生物瓣膜和/或生物补片中的应用，所述生物瓣膜包括人工主动脉瓣膜、肺动脉瓣膜、静脉瓣膜、二尖瓣膜以及三尖瓣膜。
 有益效果
所述非戊二醛可预装干燥生物瓣膜材料及其制备方法和应用，相比现有技术具有如下有益效果：
由于本发明中采用的交联方法，各步骤均没有使用戊二醛，可以从根本上避免现有戊二醛交联心包膜的戊二醛醛基残留问题；本发明采用基于基丙烯酸缩水甘油酯或甲基丙烯酸酐修饰的心包膜的双键聚合交联、碳二亚胺及多酚化合物的复合交联，将生物瓣膜开发成为脱离戊二醛溶液保存的干燥介入生物瓣膜，并预先装载于瓣膜输送系统当中，相比于戊二醛交联的心包膜，具有更好的抗钙化性能以及弹性蛋白稳定性，以及干燥瓣膜材料压握后快速展平性能，解决了现有生物瓣膜由于易钙化、无法保护弹性蛋白而导致的寿命较短的问题，延长其使用寿命，对于生物心脏瓣膜的科学研究以及相关产业化应用的发展具有重大的意义。
 附图说明
为了更清楚地说明本发明实施例的技术方案，下面将对实施例中所需要使用的附图作简单地介绍，应当理解，以下附图仅示出了本发明的某些实施例，因此不应被看作是对范围的限定，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他相关的附图。
图1为弹性蛋白酶降解失重率图；
图2为钙元素含量图；
图3为相对内皮细胞粘附率图；
图4为浸水展平测试结果图。
 本发明的实施方式
为了使本发明的目的、技术方案及优点更加清楚明白，以下结合附图及实施例，对本发明进行进一步详细说明。应当理解，此处所描述的具体实施例仅用以解释本发明，并不用于限定本发明，即所描述的实施例仅仅是本发明一部分实施例，而不是全部的实施例。通常在此处附图中描述和出示的本发明实施例的组件可以以各种不同的配置来布置和设计。
因此，以下对在附图中提供的本发明的实施例的详细描述并非旨在限制要求保护的本发明的范围，而是仅仅表示本发明的选定实施例。基于本发明的实施例，本领域技术人员在没有做出创造性劳动的前提下所获得的所有其他实施例，都属于本发明保护的范围。
需要说明的是，术语“第一”和“第二”等之类的关系术语仅仅用来将一个实体或者操作与另一个实体或操作区分开来，而不一定要求或者暗示这些实体或操作之间存在任何这种实际的关系或者顺序。而且，术语“包括”、“包含”或者其任何其他变体意在涵盖非排他性的包含，从而使得包括一系列要素的过程、方法、物品或者设备不仅包括那些要素，而且还包括没有明确列出的其他要素，或者是还包括为这种过程、方法、物品或者设备所固有的要素。在没有更多限制的情况下，由语句“包括一个……”限定的要素，并不排除在包括所述要素的过程、方法、物品或者设备中还存在另外的相同要素。
以下结合实施例对本发明的特征和性能作进一步的详细描述。
实施例1
本发明较佳实施例提供的一种功能化生物基质材料的制备方法，具体步骤如下：
1.获取新鲜的猪心包膜，并于4℃湿润状态下保存；
2.将动物组织材料浸泡在0.1%EDTA溶液中1小时，再浸泡在0.1%SDS溶液中24小时进行脱细胞处理，制成脱细胞基质；
3.采用蒸馏水与酒精体积比为1：1配制的清洗液，于室温下超声清洗，将脱细胞基质清洗干净；
4.将清洗过的脱细胞基质浸泡于浓度为1wt%甲基丙烯酸酐水溶液当中25℃反应24小时；
5.将上述材料采用上述的清洗液，于室温下超声清洗清洗干净后，在25℃下浸泡在10mmol/L的甲基丙烯酸3-磺酸丙酯水溶液中24h；
6.加入5mM过硫酸钾，在40℃反应24小时，采用蒸馏水超声清洗，即得。
实施例2
本发明较佳实施例提供的一种功能化生物基质材料的制备方法，具体步骤如下：
1.获取新鲜的猪心包膜，并于4℃湿润状态下保存；
2.将动物组织材料浸泡在0.1%EDTA溶液中1小时，再浸泡在0.1%SDS溶液中24小时进行脱细胞处理，制成脱细胞基质；
3.采用蒸馏水与酒精体积比为1：1配制的清洗液，于室温下超声清洗，将脱细胞基质清洗干净；
4.将清洗过的脱细胞基质浸泡于浓度为5wt%甲基丙烯酸酐水溶液当中20℃反应24小时；
5.将上述材料采用上述的清洗液，于室温下超声清洗清洗干净后，在30℃下浸泡在50mmol/L的甲基丙烯酸3-磺酸丙酯水溶液中24h；
6.加入20mM过硫酸钾，在37℃反应24小时，采用蒸馏水超声清洗，即得。
实施例3
本发明较佳实施例提供的一种功能化生物基质材料的制备方法，具体步骤如下：
1.获取新鲜的猪心包膜，并于4℃湿润状态下保存；
2.将动物组织材料浸泡在0.1%EDTA溶液中1小时，再浸泡在0.1%SDS溶液中24小时进行脱细胞处理，制成脱细胞基质；
3.采用蒸馏水与酒精体积比为1：1配制的清洗液，于室温下超声清洗，将脱细胞基质清洗干净；
4.将清洗过的脱细胞基质浸泡于浓度为3wt%甲基丙烯酸酐水溶液当中30℃反应24小时；
5.将上述材料采用上述的清洗液，于室温下超声清洗清洗干净后，在37℃下浸泡在50mmol/L的甲基丙烯酸3-磺酸丙酯水溶液中24h；
6.加入20mM过硫酸钾，在20℃反应48小时，采用蒸馏水超声清洗，即得。
实施例4
本发明较佳实施例提供的一种功能化生物基质材料的制备方法，具体步骤如下：
1.获取新鲜的猪心包膜，并于4℃湿润状态下保存；
2.将动物组织材料浸泡在0.1%EDTA溶液中1小时，再浸泡在0.1%SDS溶液中24小时进行脱细胞处理，制成脱细胞基质；
3.采用蒸馏水与酒精体积比为1：1配制的清洗液，于室温下超声清洗，将脱细胞基质清洗干净；
4.将清洗过的脱细胞基质浸泡于浓度为3wt%甲基丙烯酸酐水溶液当中40℃反应18小时；
5.将上述材料采用上述的清洗液，于室温下超声清洗清洗干净后，在40℃下浸泡在200mmol/L的甲基丙烯酸3-磺酸丙酯水溶液中18h；
6.加入Irgacure 2959光引发剂，在紫外交联箱中照射10min，采用蒸馏水超声清洗，即得。
实施例5
本发明较佳实施例提供的一种功能化生物基质材料的制备方法，具体步骤如下：
1.获取新鲜的猪心包膜，并于4℃湿润状态下保存；
2.将动物组织材料浸泡在0.1%EDTA溶液中1小时，再浸泡在0.1%SDS溶液中24小时进行脱细胞处理，制成脱细胞基质；
3.采用蒸馏水与酒精体积比为1：1配制的清洗液，于室温下超声清洗，将脱细胞基质清洗干净；
4.将清洗过的脱细胞基质浸泡于浓度为1wt%甲基丙烯酸酐水溶液当中40℃反应18小时；
5.将上述材料采用上述的清洗液，于室温下超声清洗清洗干净后，在35℃下浸泡在500mmol/L的甲基丙烯酸3-磺酸丙酯水溶液中18h；
6.加入Irgacure 2959光引发剂，在紫外交联箱中照射10min，采用蒸馏水超声清洗，即得。
实施例6
本发明较佳实施例提供的一种功能化基质生物材料的制备方法，具体步骤如下：
1.获取新鲜的猪心包膜，并于4℃湿润状态下保存；
2.采用蒸馏水与酒精体积比为1：1配制的清洗液，于室温下超声清洗，将细胞外基质清洗干净；
3.将清洗过的细胞外基质浸泡于浓度为2wt％甲基丙烯酸酐水溶液当中30℃反应24小时；
4.将上述材料采用上述的清洗液，于室温下超声清洗清洗干净后，在25℃下浸泡在500mmol/L的甲基丙烯酸3-磺酸丙酯水溶液中24h；
6.加入5mM过硫酸铵，在30℃反应24小时；
7.将材料用蒸馏水超声清洗，即得。
实验例1
戊二醛组样品：
采用传统戊二醛交联制备脱细胞基质生物材料制备样品，简称戊二醛瓣：将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，再浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h，再依次浸泡在0.1vt%，0.5vt%，1vt%的戊二醛PBS溶液中交联24h。
实验组样品：
分别为实施例1-3制备得到的材料，简称杂化瓣。
空白对照组：
为脱细胞基质生物材料，简称脱细胞瓣。
1、经过弹性蛋白酶降解后，分别测戊二醛组样品、实施例1制备得到样品以及空白对照组样品的样品失重率，结果如图1所示。
由图1可知，实施例1的方法可以有效保护脱细胞基质中的弹性蛋白，潜在提高了其力学性能，延长使用寿命。这是由于根据本发明方法制备得到的生物材料通过与聚合物形成互穿网络提高交联密度，从而保护了弹性蛋白。
2、将戊二醛组样品和实施例2制备得到样品经过大鼠皮下植入30天后，分别测钙元素含量，结果如图2所示。
由图2可知，实施例2制备得到的材料钙含量远少于戊二醛组，因此，本发明方法可以有效降低钙化反应，这是由于根据本发明方法制备得到的脱细胞基质生物材料没有引入戊二醛，同时遮蔽了大部分脱细胞基质中的残基，使得脱细胞基质材料结合钙离子能力下降，从而降低了钙化反应。
3、将戊二醛组样品、实施例3制备得到样品以及空白对照组样品经过1天的内皮细胞共培养，测内皮细胞在材料上的相对粘附率，结果如图3所示。
由图3可知，本发明方法可以有效提高内皮细胞在脱细胞基质生物材料上的吸附。这是由于根据本发明方法制备得到的脱细胞基质生物材料没有引入戊二醛这种具有生物毒性的交联剂，取而代之的是一种生物相容性的交联剂，同时，引入了促进内皮细胞生长迁移的功能性单体，进一步提高了生物相容性。
实施例7
本发明较佳实施例提供的一种非戊二醛可预装干燥生物瓣膜材料的制备方法，具体步骤如下：
a.将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h。
b.将脱细胞心包膜材料浸泡于5 wt%的甲基丙烯酸缩水甘油酯溶液当中37℃孵化3d，引入碳碳双键结构。
c.将上步骤所得材料浸泡于0.1M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化24h。
d.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
e.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
f.将上步骤所得材料浸泡于0.1mM的姜黄素水溶液中室温24h，漂洗。
g.将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
实施例8
本发明较佳实施例提供的一种非戊二醛可预装干燥生物瓣膜材料的制备方法，具体步骤如下：
a.将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h。
b.将脱细胞心包膜材料浸泡于2 wt%的甲基丙烯酸缩水甘油酯溶液当中37℃孵化3d，引入碳碳双键结构。
c.将上步骤所得材料浸泡于0.1M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化24h。
d.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
e.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
f.将上步骤所得材料浸泡于0.1mM的姜黄素水溶液中室温24h，漂洗。
g.将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
实施例9
本发明较佳实施例提供的一种非戊二醛可预装干燥生物瓣膜材料的制备方法，具体步骤如下：
a.将猪心包膜浸泡于0.2wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.2wt%的十二烷基硫酸钠溶液中20h，然后在无菌PBS溶液中漂洗3h。
b.将脱细胞心包膜材料浸泡于8wt%的甲基丙烯酸缩水甘油酯溶液当中37℃孵化4d，引入碳碳双键结构。
c.将上步骤所得材料浸泡于0.2M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化24h。
d.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
e.采用50 mM碳二亚胺和15mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
f.将上步骤所得材料浸泡于1mM的原花青素水溶液中室温24h，漂洗。
g.将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
实施例10
本发明较佳实施例提供的一种非戊二醛可预装干燥生物瓣膜材料的制备方法，具体步骤如下：
a.将猪心包膜浸泡于0.3wt%的乙二胺四乙酸二钠溶液中2h，然后浸泡于0.3wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗5h。
b.将脱细胞心包膜材料浸泡于3 wt%的甲基丙烯酸酐溶液中37℃孵化40h，引入碳碳双键结构。
c.将上步骤所得材料浸泡于0.5M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化20h。
d.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
e.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡30h进行交联固定。
f.将上步骤所得材料浸泡于0.5mM的白藜芦醇水溶液中室温20h，漂洗。
g.将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
实施例11
本发明较佳实施例提供的一种非戊二醛可预装干燥生物瓣膜材料的制备方法，具体步骤如下：
a.将心包膜材料浸泡于10wt％的甲基丙烯酸缩水甘油酯溶液当中40℃孵化3d，引入碳碳双键结构。
b.将上步骤所得材料浸泡于0.5M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化24h。
c.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
d.采用60mM碳二亚胺和12mMN-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
e.将上步骤所得材料浸泡于1mM的姜黄素水溶液中室温24h，漂洗。
f.将漂洗后的材料浸泡于20vt％甘油、40vt％乙醇和40vt％异丙醇混合溶液中4h后自然风干后室温保存。
对比例1
一种生物瓣膜材料的制备步骤如下：
a.将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h。
b.将上步骤所得材料浸泡于5 wt%的甲基丙烯酸缩水甘油酯溶液当中37℃孵化3d。
c.将上步骤所得材料浸泡于0.1M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化24h。
d.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
e.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
f.对上步骤所得材料进行漂洗并将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
对比例2
一种生物瓣膜材料的制备步骤如下：
a.将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h。
b.将上步骤所得材料浸泡于2 wt%的甲基丙烯酸酐溶液当中37℃孵化24h。
c.将上步骤所得材料浸泡于0.1M的甲基丙烯酸3-磺酸丙酯水溶液当中37℃孵化24h。
d.在上步骤所得材料中加入20mM过硫酸铵和20mM亚硫酸氢钠水溶液37℃交联24h。
e.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
f.对上步骤所得材料进行漂洗并将漂洗后材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
对比例3
一种生物瓣膜材料的制备步骤如下：
a.将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h。
b.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
c.对上步骤所得材料进行漂洗并将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
对比例4
一种生物瓣膜材料的制备步骤如下：
a.将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，然后浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h。
b.采用60 mM碳二亚胺和12 mM N-羟基丁二酰亚胺混合溶液对上步骤所得材料在37℃浸泡24h进行交联固定。
c.将上步骤所得材料浸泡于0.1mM姜黄素溶液中室温24h。
d.对上步骤所得材料进行漂洗并将漂洗后的材料浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h后自然风干后室温保存。
实验例2
设置对照组与实施例7、8及对比例1-4制得的材料分别进行抗钙化性能测试，弹性蛋白稳定性测试及浸水展平测试。
对照组：将猪心包膜浸泡于0.1wt%的乙二胺四乙酸二钠溶液中1h，再浸泡于0.1wt%的十二烷基硫酸钠溶液中24h，然后在无菌PBS溶液中漂洗1h，再依次浸泡在0.1vt%，0.5vt%，1vt%的戊二醛PBS溶液中交联24h，然后浸泡于20vt%甘油、40vt%乙醇和40vt%异丙醇混合溶液中4h，自然风干后室温保存。
（1）抗钙化性能测试
将裁剪成1cm×1cm的实施例组样品、对比例组样品和对照组样品清洗好，向20天左右幼年SD大鼠大鼠腹腔注射3%戊巴比妥钠0.1 mL进行麻醉，剃除脊柱两旁肌肉上的皮毛，碘酒和酒精常规消毒。右侧背部皮下植入试验组样品1个，左侧背部皮下植入对照组样品1个，缝合皮肤切口。60天后，采用颈椎脱臼法对动物进行安乐死，取出移植物。小心除去移植物表面的宿主组织，生理盐水冲洗干净。冷冻干燥后称量干重，之后采用6N浓盐酸在95摄氏度水浴锅中消解直到无可见固体颗粒，之后采用电感耦合等离子体发射光谱仪进行钙元素的定量分析。
对实施例和对照制得的材料分别进行抗钙化性能测试，结果如下表1所示。由表1可知，实施例7和实施例8制得的材料挂钙量相比对照组大大减少，且实施例7和实施例8制得的材料挂钙量少于对比例1-4，因此，本发明的材料具有优异的抗钙化性能。
表1 挂钙量含量表
  挂钙量（μg/mg）
对照组 19.41 ± 9.88
实施例7 0.40 ± 0.05
实施例8 0.44 ± 0.04
对比例1 0.57 ± 0.31
对比例2 0.56 ± 0.40
对比例3 2.99 ± 2.32
对比例4 2.24 ± 1.40
（2）弹性蛋白稳定性测试
生物瓣膜植入体内后，会接触血液中的蛋白酶，在蛋白酶作用下，瓣膜中的胶原蛋白和弹性蛋白会发生降解，从而影响生物瓣膜稳定性。体外酶降解实验是一种检验生物瓣膜抵抗蛋白酶降解能力的有效方法。通过模拟体内蛋白酶环境，检验生物瓣膜的组分稳定性。将生物瓣膜冷冻干燥后，37℃条件下，用含有弹性蛋白酶（30 U/mL）的Tris buffer（0.1 M Tris，1 mM CaCl2, pH = 7.8）溶液中孵育24h冲洗并冷冻干燥后称重，计算干重损失率。
弹性蛋白稳定性结果如下表2所示。由下表2可知，实施例7和实施例8的弹性蛋白酶降解失重率相对于对照组大大减少，而对比例2、3和4的弹性蛋白酶降解失重率仅相对于对照组略微减少，综上，本发明制得的材料弹性蛋白稳定性大大提高。
表2 弹性蛋白稳定性表
  弹性蛋白酶降解失重率%
对照组 12.48 ± 0.44
实施例7 6.36 ± 0.04
实施例8 8.45 ± 0.49
对比例1 6.48 ± 0.32
对比例2 10.16 ± 0.33
对比例3 11.16 ± 0.32
对比例4 11.44 ± 0.36
（3）浸水展平测试
分别对实施例7、8，对比例1-4以及对照组中制得的材料进行折压浸水测试，具体测试如下：采用5mm内径的塑料管进行模拟折压测试，每组材料用剪刀裁剪面积大小约为3cm*3cm的方形样品，用镊子慢慢将方形样品塞入5mm内径的塑料管，然后在温度为40℃，湿度为60%-80%的恒温恒湿箱中放置72h，之后将材料挤出塑料管并浸泡在PBS缓冲液中，观察并拍照记录浸水展平情况。
浸水展平如图4所示，实施例以及对比组的浸水展平情况均较好，而（戊二醛）对照组无法快速展平，折痕较明显。
以上所述仅为本发明的较佳实施例而已，并不用以限制本发明，凡在本发明的精神和原则之内所作的任何修改、等同替换和改进等，均应包含在本发明的保护范围之内。

Claims (30)

  1. 一种功能化生物基质材料的制备方法，其特征在于，包括以下步骤：
    将生物基质材料清洗后，浸泡在甲基丙烯酸缩水甘油酯或甲基丙烯酸酐水溶液中，然后再浸泡在甲基丙烯酸3-磺酸丙酯水溶液中，之后加入引发剂引发聚合反应。
  2. 根据权利要求1所述的功能化生物基质材料的制备方法，其特征在于，所述生物基质材料为经过脱细胞处理的动物组织，所述动物组织来源于猪、牛或羊；所述动物组织包括血管、心脏瓣膜和心包膜，其主要成分为胶原蛋白、弹性蛋白和糖胺多糖中的至少一种。
  3. 根据权利要求1或2所述的功能化生物基质材料的制备方法，其特征在于，所述甲基丙烯酸酐水溶液的浓度为1-20wt%。
  4. 根据权利要求1或2所述的功能化生物基质材料的制备方法，其特征在于，所述清洗后的生物基质材料在4-60℃下浸泡在甲基丙烯酸酐水溶液中反应6-72h。
  5. 根据权利要求1或2所述的功能化生物基质材料的制备方法，其特征在于，所述甲基丙烯酸3-磺酸丙酯水溶液浓度为10-500mmol/L。
  6. 根据权利要求1或2所述的功能化生物基质材料的制备方法，其特征在于，在4-60℃下于甲基丙烯酸3-磺酸丙酯水溶液中浸泡2-72h。
  7. 根据权利要求1或2所述的功能化生物基质材料的制备方法，其特征在于，所述引发剂为光引发剂或热引发剂；所述光引发剂为过硫酸钾、过硫酸钠和过硫酸铵中的至少一种，所述热引发剂为2-羟基-2-甲基-1-苯基丙酮、1-羟基环己基苯基甲酮、2-甲基-2-(4-吗啉基)-1-[4-(甲硫基)苯基]-1-丙酮、2-羟基-4'-(2-羟乙氧基)-2-甲基苯丙酮、2,4,6-三甲基苯甲酰基-二苯基氧化膦和2-羟基-2-甲基-1-[4-(2-羟基乙氧基)苯基]-1-丙酮中的至少一种。
  8. 根据权利要求7所述的功能化生物基质材料的制备方法，其特征在于，采用所述热引发剂时反应条件为在20-45℃下聚合反应18-48h；采用所述光引发剂时反应条件为在紫外光源下于室温中反应5-30min。
  9. 根据权利要求1所述的功能化生物基质材料的制备方法，其特征在于，所述制备方法还包括在引发聚合反应后，进行以下步骤：
    采用碳二亚胺和N-羟基丁二酰亚胺混合溶液对聚合反应后所得材料进行交联固定；
    将交联固定所得材料浸泡于多酚溶液中。
  10. 根据权利要求9所述的功能化生物基质材料的制备方法，其特征在于，将经多酚溶液浸泡处理后的材料漂洗，采用抑菌溶剂保存或采用醇溶液脱水干燥后保存。
  11. 根据权利要求10所述的功能化生物基质材料的制备方法，其特征在于，所述醇溶液为甘油与乙醇混合溶液或甘油、乙醇与异丙醇的混合溶液。
  12. 根据权利要求10所述的功能化生物基质材料的制备方法，其特征在于，所述醇溶液为10-30vt%甘油与70-90vt%乙醇混合溶液或10-30vt%甘油、35-45vt%乙醇与35-45vt%异丙醇混合溶液。
  13. 根据权利要求1所述的功能化生物基质材料的制备方法，其特征在于，所述加入引发剂引发聚合反应，具体步骤包括：
    在20-45℃的条件下热引发双键聚合反应12-48h；其中，引发剂为过硫酸钾、过硫酸铵、亚硫酸氢钠和四甲基乙二胺中的至少一种。
  14. 根据权利要求9所述的功能化生物基质材料的制备方法，其特征在于，将交联固定所得材料浸泡于多酚溶液中具体步骤包括：
    将交联固定后材料于0.01-10 mM多酚类化合物水溶液中浸泡1-24h；多酚类化合物为姜黄素、原花青素、槲皮素、白藜芦醇、芦荟素、芦荟大黄素、单宁酸、表没食子儿茶素没食子酸酯、五没食子酰葡萄糖和京尼平中的至少一种。
  15. 采用权利要求1-14中任一项所述的方法制备得到的功能化生物基质材料。
  16. 根据权利要求15所述的功能化生物基质材料在制备医用材料中的应用，所述医用材料为开胸生物瓣膜、介入生物瓣膜、组织工程瓣膜、生物补片、人工血管或组织工程血管。
  17. 一种非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，包括以下步骤：
    a.获取动物心包膜材料；
    b.将心包膜材料浸泡在甲基丙烯酸缩水甘油酯或丙烯酸酐溶液中，以引入碳碳双键结构；
    c.将经步骤b处理的材料浸泡在甲基丙烯酸3-磺酸丙酯水溶液中；
    d.在经步骤c处理的材料中加入引发剂进行双键聚合交联；
    e.采用碳二亚胺和N-羟基丁二酰亚胺混合溶液对步骤d所得材料进行交联固定；
    f.将步骤e所得材料浸泡于多酚溶液中；
    g.将经步骤f处理的材料漂洗，采用抑菌溶剂保存或采用醇溶液脱水干燥后保存，即得。
  18. 根据权利要求17所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤a包括将动物心包膜材料脱细胞。
  19. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤a中动物心包膜材料取自猪、牛或羊。
  20. 根据权利要求18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤a中脱细胞具体为：将心包膜于0.01-1wt%的乙二胺四乙酸二钠溶液中浸泡1-4h，再于0.01-1wt%的十二烷基硫酸钠溶液中浸泡1-24h，然后在无菌PBS溶液中漂洗1-24h。
  21. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤b具体为：在25-45℃下将心包膜于1-10wt%的甲基丙烯酸缩水甘油酯溶液中浸泡3-7d，或于1-5 wt%的甲基丙烯酸酐水溶液中浸泡12-48h。
  22. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤c具体为：在25-45℃下将材料于0.01-1M的甲基丙烯酸3-磺酸丙酯水溶液中浸泡12-48h。
  23. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤d具体为：在20-45℃的条件下热引发双键聚合反应12-48h；其中，引发剂为过硫酸钾、过硫酸铵、亚硫酸氢钠和四甲基乙二胺中的至少一种。
  24. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤e具体为：在25-45℃下将双键聚合交联处理后的材料在10-60 mM碳二亚胺和1-20 mM N-羟基丁二酰亚胺的水混合pH缓冲溶液中浸泡24-48h。
  25. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤f具体为：将交联固定后材料于0.01-10 mM多酚类化合物水溶液中浸泡1-24h；其中，多酚类化合物为姜黄素、原花青素、槲皮素、白藜芦醇、芦荟素、芦荟大黄素、单宁酸、表没食子儿茶素没食子酸酯、五没食子酰葡萄糖和京尼平中的至少一种。
  26. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述醇溶液为甘油与乙醇混合溶液或甘油、乙醇与异丙醇的混合溶液。
  27. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述醇溶液为10-30vt%甘油与70-90vt%乙醇混合溶液或10-30vt%甘油、35-45vt%乙醇与35-45vt%异丙醇混合溶液。
  28. 根据权利要求17或18所述的非戊二醛可预装干燥生物瓣膜材料的制备方法，其特征在于，所述步骤d具体为：在20-45℃的条件下热引发双键聚合反应12-48h；其中，引发剂为过硫酸钾、过硫酸铵、亚硫酸氢钠和四甲基乙二胺中的至少一种。
  29. 根据权利要求17-28中任一项所述的方法制备得到的非戊二醛可预装干燥生物瓣膜材料。
  30. 根据权利要求29所述的非戊二醛可预装干燥生物瓣膜材料在制备生物瓣膜和/或生物补片中的应用，所述生物瓣膜包括人工主动脉瓣膜、肺动脉瓣膜、静脉瓣膜、二尖瓣膜以及三尖瓣膜。
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