CN107349456B - Preparation method of collagen sponge with pore size self-adaptive adjusting capacity and collagen sponge - Google Patents
Preparation method of collagen sponge with pore size self-adaptive adjusting capacity and collagen sponge Download PDFInfo
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- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/42—Use of materials characterised by their function or physical properties
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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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing macromolecular materials
- A61L15/32—Proteins, polypeptides; Degradation products or derivatives thereof, e.g. albumin, collagen, fibrin, gelatin
- A61L15/325—Collagen
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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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/42—Use of materials characterised by their function or physical properties
- A61L15/425—Porous materials, e.g. foams or sponges
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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
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/42—Use of materials characterised by their function or physical properties
- A61L15/62—Compostable, hydrosoluble or hydrodegradable materials
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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
- A61L27/14—Macromolecular materials
- A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
- A61L27/24—Collagen
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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
- A61L27/50—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
- A61L27/56—Porous materials, e.g. foams or sponges
-
- 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
- A61L27/58—Materials at least partially resorbable by the body
-
- 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
- A61L27/60—Materials for use in artificial skin
Abstract
The invention discloses a preparation method of collagen sponge with pore size self-adaptive regulating capacity and collagen sponge, which comprises the steps of dissolving natural collagen by using a first acetic acid aqueous solution under an ice bath condition, and regulating the pH value of the collagen solution to 6-8 to obtain a first collagen solution; adding a glutaraldehyde aqueous solution into the first collagen solution, culturing at constant temperature, and standing to obtain collagen; transferring the collagen gel into a distilled water solution for rinsing, removing glutaraldehyde, and freeze-drying to obtain a macroporous collagen sponge frame; dissolving natural collagen with a second acetic acid aqueous solution to obtain a second collagen solution; placing the macroporous collagen sponge frame in a second collagen solution, infiltrating under vacuum, draining, freeze-drying to obtain primary collagen sponge, placing the primary collagen sponge in the second collagen solution again, infiltrating under vacuum, draining, freeze-drying to obtain collagen sponge; the collagen sponge can intelligently adapt to the requirements of different application stages on the mechanical property, compactness and gap size of the material.
Description
Technical Field
The invention belongs to the technical field of medical biomaterials, and particularly relates to a preparation method of a collagen sponge with self-adaptive pore size adjusting capability and the collagen sponge.
Background
Collagen is the most abundant and widely distributed structural protein in mammals. Collagen, together with components such as polysaccharides, which are the main components of extracellular matrices, constitute an extracellular microenvironment (extracellular matrix) with high cell affinity and moderate strength, providing an indispensable biological site for proliferation, migration, and metabolism of cells. Meanwhile, collagen also participates in the construction of organs such as skin, achilles tendon, cornea, blood vessel and the like in the form of fibers, fiber bundles and the like and plays an important biological function. Because collagen has excellent biocompatibility, degradability and good biomechanical property, the collagen is widely applied to the fields of biomedical materials, medical tissue engineering, medical cosmetology and the like in recent years. In these fields, collagen is generally used as a biological scaffold material, a cavity filling material, a drug carrier material or an extracellular matrix supplement material, and is used for wound covering and healing promotion, artificial organ construction, drug slow release, skin beauty and wrinkle removal and the like. The collagen sponge is a collagen medical product which is most widely applied, and is mainly used in clinical fields of wound surface hemostasis, cavity filling, wound healing promotion, burn and scald wound surface covering, missing skin tissue regeneration promotion and the like. Generally, the manufacturing process of collagen sponge includes the steps of collagen extraction, purification, concentration, crosslinking, and freeze-drying molding, sterilization, and packaging.
The properties of collagen sponges are closely related to the manufacturing process. The higher the concentration of the collagen solution is, the more compact the gap and the smaller the pore diameter of the dried collagen sponge are, and the stronger the shape stability and the tensile resistance of the sponge material are. Chemical crosslinking or fiber restructuring techniques are often used to improve the biostability (thermal stability, resistance to enzymatic degradation) of collagen sponges to meet the requirements of the sponge product application. Wherein, the chemical crosslinking method can form covalent bond crosslinking in collagen molecules or among molecules, thereby greatly improving the biological stability of the collagen; the fiber recombination technology utilizes the specific molecular self-assembly performance of collagen and improves the biostability of collagen products by a method of promoting collagen molecular fibrosis under appropriate conditions.
In clinical application, the performance indexes of the collagen sponge products not only require biological safety and functional effectiveness, but also require the products to have good shape stability, mechanical property and degradability. To ensure the functional continuity of the product, the collagen sponge is also required to have suitable degradation resistance. In the application of promoting wound healing and skin tissue regeneration, the collagen sponge is particularly emphasized to have good cell proliferation and tissue regeneration promoting capacity. A large number of researches prove that the healing and regeneration of the tissue wound surface are closely related to cell proliferation, and the gap structure of a cell adhesion microenvironment is closely related to the cell proliferation capacity. The most predominant fibroblasts in skin tissue are spindle-shaped, about 50-80 μm in length and 5-15 μm in diameter. Therefore, the ideal physical size of the gap of the biological dressing for promoting cell proliferation is more than 100 μm to provide a proper space for proliferation, migration and metabolism of fibroblasts. However, too large a void size tends to result in a material having a small specific surface area and insufficient cell attachment space, and also directly results in a material having a significantly reduced mechanical strength and a poor shape stability and handleability. At present, the collagen sponge is usually prepared by chemically crosslinking a high-concentration collagen solution and freeze-drying to form pores. The preparation process can effectively enhance the mechanical property, the shape stability and the degradation resistance of the material by increasing the concentration of collagen and introducing chemical crosslinking. However, due to the excessive concentration of collagen and the molecular aggregation and contraction effect caused by chemical crosslinking, the material has compact pores, and the size of the pores is too small (generally less than 50 μm), so that the size of the pores required by cell proliferation and migration cannot be well met.
Disclosure of Invention
The invention aims to provide a preparation method of a collagen sponge material which can give consideration to mechanical properties, appropriate degradation resistance and appropriate gap structure of the material so as to meet the requirements of medical materials such as medical dressings, skin substitutes for burns and scalds and the like on various properties of products.
In order to achieve the above object, an aspect of the present invention provides a method for preparing a collagen sponge having a pore size adaptive modulation ability, the method comprising:
(1) under the ice-bath condition, dissolving natural collagen by using a first acetic acid aqueous solution, and adjusting the pH value of the collagen solution to 6-8 to obtain a first collagen solution;
(2) adding a glutaraldehyde aqueous solution into the first collagen solution, uniformly mixing, culturing at a constant temperature, and standing to obtain a fibrillated and chemically crosslinked collagen;
(3) transferring the collagen gel into a distilled water solution for repeated rinsing to remove glutaraldehyde which does not participate in the reaction, and then freeze-drying to obtain a macroporous collagen sponge frame;
(4) dissolving natural collagen with a second acetic acid aqueous solution to obtain a second collagen solution;
(5) and placing the macroporous collagen sponge framework into the second collagen solution, infiltrating under the condition of vacuumizing, draining, freezing and drying to obtain primary collagen sponge, placing the primary collagen sponge into the second collagen solution again, infiltrating under the condition of vacuumizing, draining, freezing and drying to obtain the collagen sponge.
The invention also provides the collagen sponge prepared by the preparation method of the collagen sponge with the pore size adaptive regulation capacity.
The technical scheme of the invention has the following advantages:
(1) according to the invention, high-concentration collagen is introduced into the macroporous collagen sponge frame twice, so that the compactness of the sponge material is enhanced, the mechanical strength, the form stability and the application operability of the material are improved, and a good isolation effect and a larger cell attachment area are favorably provided for a wound surface at the initial stage of use; on the other hand, in the middle and later stages of product use, the introduced collagen which is not chemically crosslinked can be rapidly degraded under the action of endogenous enzymes, the original crosslinked macroporous collagen sponge framework is still remained, and the formed macroporous structure can continuously provide a proper biological space for the proliferation and migration of subsequent cells;
(2) the results of in vitro proliferation experiments of fibroblasts show that when cells are cultured for 7 days, compared with common collagen sponges, the fibroblast proliferation rate in the collagen sponge material prepared by the method is obviously improved;
(3) compared with the common collagen sponge, the collagen sponge disclosed by the invention can intelligently adapt to the requirements of different application stages on the mechanical property, compactness and gap size of the material, can better meet the technical requirements of products in clinical medicine, and has a good application prospect.
Additional features and advantages of the invention will be set forth in the detailed description which follows.
Drawings
The above and other objects, features and advantages of the present invention will become more apparent by describing in more detail exemplary embodiments thereof with reference to the attached drawings.
FIG. 1a shows a scanning electron microscope observation of the microstructure of a macroporous collagen sponge framework according to one embodiment of the present invention.
FIG. 1b shows a scanning electron microscope observation of the microstructure of a collagen sponge according to one embodiment of the present invention.
FIG. 1c shows a scanning electron micrograph of the microstructure of the sponge product of comparative example 1.
FIG. 1d shows a scanning electron micrograph of the microstructure of the sponge product of comparative example 2.
FIG. 2 is a graph showing experimental data on tensile resistance of collagen sponge products according to examples and comparative examples of the present invention.
Fig. 3 shows a graph of experimental data for in vitro enzymatic degradation of collagen sponge products in collagenase solutions according to example 1 of the present invention and a comparative example.
Fig. 4 is a graph showing data of MTT cell proliferation experiments for collagen sponge products according to examples of the present invention and comparative examples.
Detailed Description
Preferred embodiments of the present invention will be described in more detail below. While the following describes preferred embodiments of the present invention, it should be understood that the present invention may be embodied in various forms and should not be limited by the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
One aspect of the present invention provides a method for preparing a collagen sponge having a pore size adaptive modulation ability, the method comprising:
(1) under the ice-bath condition, dissolving natural collagen by using a first acetic acid aqueous solution, and adjusting the pH value of the collagen solution to 6-8 to obtain a first collagen solution;
(2) adding a glutaraldehyde aqueous solution into the first collagen solution, uniformly mixing, culturing at a constant temperature, and standing to obtain a fibrillated and chemically crosslinked collagen;
(3) transferring the collagen gel into a distilled water solution for repeated rinsing to remove glutaraldehyde which does not participate in the reaction, and then freeze-drying to obtain a macroporous collagen sponge frame;
(4) dissolving natural collagen with a second acetic acid aqueous solution to obtain a second collagen solution;
(5) and placing the macroporous collagen sponge framework into the second collagen solution, infiltrating under the condition of vacuumizing, draining, freezing and drying to obtain primary collagen sponge, placing the primary collagen sponge into the second collagen solution again, infiltrating under the condition of vacuumizing, draining, freezing and drying to obtain the collagen sponge.
Different from the existing collagen sponge manufacturing process, the invention adopts a two-step method to prepare the collagen sponge. Firstly, using a collagen solution with a lower concentration as a raw material, and combining collagen fibrillation and chemical crosslinking steps to obtain a macroporous collagen sponge frame with a larger gap structure and good degradation resistance; then, high-concentration collagen is introduced into the macroporous collagen sponge framework to fill original macropores, and a compact collagen sponge material with larger specific surface area and good mechanical strength is formed.
Preferably, the pore diameter of the macroporous collagen sponge framework is more than 100 μm.
Preferably, the freeze-drying process conditions in step (3) and step (5) include: pre-freezing collagen gel or soaked macroporous collagen sponge frame at-60 deg.C for 12-24 hr, and vacuum-pumping to absolute pressure of 2-20Pa for drying for 48-96 hr to complete sublimation of water molecules.
According to the present invention, preferably, the concentration of the first collagen solution is 1-5 mg/mL.
According to the present invention, preferably, the method for adjusting the pH of the collagen solution is dialysis with a phosphate buffer solution. Adjusting the pH value of the collagen solution to 2-6 deg.C.
According to the present invention, preferably, in the step (2), the glutaraldehyde aqueous solution is added to a concentration of glutaraldehyde in the first collagen solution of 0.05-0.20 wt%. The concentration of the aqueous glutaraldehyde solution is preferably 5 wt%.
According to the invention, preferably, the temperature of the constant temperature culture is 25-40 ℃, and the standing time is 12-48 h.
Preferably, the isothermal cultivation is carried out in a water bath or an incubator.
According to the invention, preferably, the concentration of the second collagen solution is between 8 and 15 mg/mL.
According to the present invention, preferably, the step (5) conditions include: the vacuum degree is 0.08-0.1MPa, and the infiltration time is 0.5-2 h.
According to the present invention, preferably, the native collagen is type i collagen.
The natural collagen comprises collagen extracted, separated and purified from mammals, fishes, amphibians and poultry. The natural collagen is preferably type I collagen of grass carp skin, type I collagen of bovine achilles tendon, type I collagen of pigskin, type I collagen of bullfrog, and the like.
According to the invention, preferably, the concentration of the first aqueous acetic acid solution is 0.05-0.3mol/L, and the concentration of the second aqueous acetic acid solution is 0.4-0.6 mol/L.
The invention also provides the collagen sponge prepared by the preparation method of the collagen sponge with the pore size adaptive regulation capacity.
Compared with the common collagen sponge, the collagen sponge disclosed by the invention can intelligently adapt to the requirements of different application stages on the mechanical property, compactness and gap size of the material, can better meet the technical requirements of products in clinical medicine, and has a good application prospect.
The invention is further illustrated by the following examples:
example 1
Dissolving type I collagen extracted from grass carp skin with 0.1mol/L acetic acid water solution under ice bath condition, dialyzing phosphate buffer solution at 4 deg.C to adjust pH of collagen solution to 7.0 to obtain first collagen solution with concentration of 2 mg/mL; adding a glutaraldehyde water solution with the concentration of 5 wt% into the first collagen solution until the concentration of glutaraldehyde in the first collagen solution is 0.1%, uniformly mixing, placing in a constant-temperature incubator at 25 ℃, and standing for 12 hours to obtain fibrillated and chemically crosslinked collagen; transferring the collagen gel into a distilled water solution for repeated rinsing to remove glutaraldehyde which does not participate in the reaction, and then freeze-drying to obtain a macroporous collagen sponge framework for later use (as shown in figure 1 a), wherein the pore diameter of the macroporous collagen sponge framework is larger than 100 microns; dissolving grass carp collagen by using 0.5mol/L acetic acid aqueous solution to obtain a second collagen solution with the concentration of 8 mg/mL; soaking the macroporous collagen sponge frame in 8mg/mL second collagen solution for 1 hour in a vacuum drier, vacuumizing at the vacuum degree of 0.09MPa, removing air from the gap of the macroporous collagen sponge frame and promoting the introduction of the collagen solution, draining, and freeze-drying to obtain primary collagen sponge; soaking the primary collagen sponge in 8mg/mL second collagen solution for 1 hr, vacuumizing at 0.09MPa, draining, and freeze-drying to obtain collagen sponge (shown in FIG. 1 b); the freeze drying is to pre-freeze the collagen or the soaked macroporous collagen sponge frame for 18 hours at-60 ℃, and then to dry for 72 hours under the condition of the absolute pressure of 10Pa by vacuumizing, so as to complete the sublimation of water molecules.
Example 2
Dissolving type I collagen extracted from bovine Achilles tendon in 0.1mol/L acetic acid aqueous solution under ice bath condition, and dialyzing phosphate buffer solution at 4 deg.C to adjust pH of collagen solution to 7.0 to obtain a first collagen solution with concentration of 5 mg/mL; adding a glutaraldehyde water solution with the concentration of 5 wt% into the first collagen solution until the concentration of glutaraldehyde in the first collagen solution is 0.1 wt%, uniformly mixing, placing in a water bath at 35 ℃, and standing for 48 hours to obtain a fibrillated and chemically crosslinked collagen; transferring the collagen gel into a distilled water solution for repeated rinsing to remove glutaraldehyde which does not participate in the reaction, and then freeze-drying to obtain a macroporous collagen sponge framework for later use, wherein the pore diameter of the macroporous collagen sponge framework is larger than 100 mu m; dissolving bovine achilles tendon collagen by using 0.5mol/L acetic acid aqueous solution to obtain a second collagen solution with the concentration of 13 mg/mL; immersing the macroporous collagen sponge frame into 13mg/mL second collagen solution in a vacuum drier, soaking for 1 hour, vacuumizing at the vacuum degree of 0.09MPa, removing air in gaps of the macroporous collagen sponge frame and promoting the introduction of the collagen solution, draining, and freeze-drying to obtain primary collagen sponge; immersing the primary collagen sponge into 13mg/mL second collagen solution again, infiltrating for 1 hour, vacuumizing at the same time, wherein the vacuum degree is 0.09MPa, draining, and freeze-drying to obtain the collagen sponge; the freeze drying is to pre-freeze the collagen or the soaked macroporous collagen sponge frame for 18 hours at-60 ℃, and then to dry for 72 hours under the condition of the absolute pressure of 10Pa by vacuumizing, so as to complete the sublimation of water molecules.
Comparative example 1
Dissolving type I collagen extracted from bovine Achilles tendon in 0.5mol/L acetic acid aqueous solution to obtain collagen solution with collagen concentration of 13mg/mL, and freeze drying to obtain collagen sponge without chemical crosslinking treatment (shown in FIG. 1 c).
Comparative example 2
Dissolving type I collagen extracted from bovine Achilles tendon with 0.5mol/L acetic acid aqueous solution to obtain collagen solution with collagen concentration of 13mg/mL, adding 5 wt% glutaraldehyde aqueous solution into the collagen solution until the concentration of glutaraldehyde in the collagen solution is 0.1%, mixing uniformly, and standing and crosslinking the collagen solution for 12 hours. The cross-linked collagen obtained was rinsed with distilled water repeatedly to remove residual glutaraldehyde, and then freeze-dried to obtain a chemically cross-linked collagen sponge (as shown in FIG. 1 d).
Test example 1
The collagen sponge products of example 1, comparative example 1, and comparative example 2, and the macroporous collagen sponge framework of example 1 were subjected to electron microscope scanning to obtain a scanning electron microscope observation image of the microstructure of each collagen sponge product.
As shown in fig. 1a to 1d, the collagen sponge framework prepared by using a low concentration in example 1 has a large and loose void structure, and after a high concentration collagen solution is introduced, the void of the prepared collagen sponge product is significantly reduced, dense and uniformly distributed, and the void structure is closer to that of comparative example 1 and comparative example 2.
Test example 2
FIG. 2 is a graph showing tensile test data for collagen sponge products according to examples and comparative examples of the present invention, wherein the number of samples n of each material tested is 3.
Tensile experiments were performed on the collagen sponge products of examples and comparative examples.
As shown in FIG. 2, the tensile strength of the sample of comparative example 1, which was not chemically cross-linked, was the lowest, while the tensile strength of the collagen sample of comparative example 2, which was cross-linked with glutaraldehyde, was significantly improved. The tensile strength of the collagen sponges prepared in the examples 1 and 2 is close to that of the collagen sponge prepared in the comparative example 2.
Test example 3
In vitro enzymatic degradation test experiments were performed on the collagen sponge products prepared in example 1, comparative example 1 and comparative example 2.
As shown in fig. 3, comparative example 1 has a fast hydrolysis rate in collagenase solution and shows a continuous hydrolysis state since it is not cross-linked with glutaraldehyde; in contrast, in comparative example 2, the hydrolysis rate was significantly reduced, although the hydrolysis was still sustained due to the glutaraldehyde crosslinking treatment; unlike the comparative example, the sample of example 1 exhibited a distinct stepwise hydrolysis behavior, with a faster hydrolysis rate in the early stage, which is a degradation phenomenon of the introduced, uncrosslinked collagen, and a significantly reduced degradation rate in the later stage, which is a degradation behavior of the crosslinked collagen in the collagen sponge framework.
Test example 4
Fibroblast proliferation experiments were performed on examples and comparative examples, in which fibroblasts were rat tail NIH3T3 cells, cultured for 7 days, and the number of samples n was 8.
As shown in FIG. 4, the cell proliferation promoting ability of both example 1 and example 2 was significantly enhanced (p < 0.01) as compared with the comparative example, indicating that the preparation method had a significant effect.
Having described embodiments of the present invention, the foregoing description is intended to be exemplary, not exhaustive, and not limited to the embodiments disclosed. Many modifications and variations will be apparent to those of ordinary skill in the art without departing from the scope and spirit of the described embodiments.
Claims (8)
1. A preparation method of collagen sponge with pore size adaptive regulation capability is characterized by comprising the following steps:
(1) under the ice-bath condition, dissolving natural collagen by using a first acetic acid aqueous solution, and adjusting the pH value of the collagen solution to 6-8 to obtain a first collagen solution;
(2) adding a glutaraldehyde aqueous solution into the first collagen solution, uniformly mixing, culturing at a constant temperature, and standing to obtain a fibrillated and chemically crosslinked collagen;
(3) transferring the collagen gel into a distilled water solution for repeated rinsing to remove glutaraldehyde which does not participate in the reaction, and then freeze-drying to obtain a macroporous collagen sponge frame;
(4) dissolving natural collagen with a second acetic acid aqueous solution to obtain a second collagen solution;
(5) placing the macroporous collagen sponge framework into the second collagen solution, infiltrating under a vacuum condition, draining, freezing and drying to obtain primary collagen sponge, placing the primary collagen sponge into the second collagen solution again, infiltrating under the vacuum condition, draining, freezing and drying to obtain collagen sponge;
wherein the concentration of the first collagen solution is 1-5 mg/mL; the concentration of the second collagen solution is 8-15 mg/mL; the pore diameter of the macroporous collagen sponge framework is larger than 100 mu m.
2. A method for preparing a collagen sponge having adaptive pore size modulating ability as claimed in claim 1, wherein the method for adjusting pH of collagen solution is dialysis with phosphate buffer solution.
3. The method for preparing a collagen sponge having adaptive porosity and size adjustment capability according to claim 1, wherein the glutaraldehyde solution is added to the first collagen solution in step (2) to a concentration of 0.05-0.20 wt% glutaraldehyde.
4. The method for preparing a collagen sponge having adaptive porosity and size adjustment capability according to claim 1, wherein the incubation temperature is 25-40 ℃ and the standing time is 12-48 h.
5. The method for preparing a collagen sponge having adaptive pore size modulating ability according to claim 1, wherein the step (5) conditions include: the vacuum degree is 0.08-0.1MPa, and the infiltration time is 0.5-2 h.
6. The method for preparing a collagen sponge having adaptive pore size modulating ability as claimed in claim 1, wherein the native collagen is type I collagen.
7. The method for preparing a collagen sponge having adaptive pore size modulating ability according to claim 1, wherein the concentration of the first aqueous acetic acid solution is 0.05-0.3mol/L and the concentration of the second aqueous acetic acid solution is 0.4-0.6 mol/L.
8. A collagen sponge prepared by the method for preparing a collagen sponge having adaptive porosity and size control ability according to any one of claims 1 to 7.
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| CN116772523B (en) * | 2023-08-25 | 2023-11-10 | 北京国械堂科技发展有限责任公司 | Freeze-drying method of collagen sponge |
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| CN101224311B (en) * | 2008-02-01 | 2011-10-05 | 北京工业大学 | Preparing method of compound collagen hemostatic material |
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