WO2011071074A1 - 多孔性部材、多孔化方法および前記多孔性部材の製造方法 - Google Patents
多孔性部材、多孔化方法および前記多孔性部材の製造方法 Download PDFInfo
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- WO2011071074A1 WO2011071074A1 PCT/JP2010/072009 JP2010072009W WO2011071074A1 WO 2011071074 A1 WO2011071074 A1 WO 2011071074A1 JP 2010072009 W JP2010072009 W JP 2010072009W WO 2011071074 A1 WO2011071074 A1 WO 2011071074A1
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- porous member
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Classifications
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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
- A61L27/56—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
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/14—Macromolecular materials
- A61L27/18—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
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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
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/04—Macromolecular materials
- A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
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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
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L31/146—Porous materials, e.g. foams or sponges
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
- Y10T428/1376—Foam or porous material containing
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
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- Y10T428/00—Stock material or miscellaneous articles
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- Y10T428/249953—Composite having voids in a component [e.g., porous, cellular, etc.]
Definitions
- the present invention relates to a porous member, a porous method, and a method for manufacturing the porous member. More specifically, for example, the present invention relates to a porous member serving as a biological member such as a cell scaffold material or a stent.
- the scaffold material In the field of cell engineering and regenerative medical engineering, cells are proliferated using scaffold materials for the purpose of tissue regeneration and the like.
- the scaffold material In general, the scaffold material is required to have a porous structure for the purpose of holding the seeded cells, and to have an appropriate rigidity for the purpose of maintaining the overall shape.
- the scaffold material exhibits flexibility by having the porous structure, but on the other hand, sufficient rigidity may not be obtained. Therefore, in recent years, there has been a demand for providing a scaffold material having both structural characteristics such as porosity and physical characteristics such as rigidity.
- a laminate of a porous member imparting a porous structure and a core member imparting rigidity has been proposed.
- a paste method is known (Patent Document 1).
- the paste method is a method of laminating the porous member and the core member by, for example, heat treatment, solvent treatment, adhesion treatment using an adhesive, or the like.
- heat treatment or the solvent treatment one surface of the porous member or the core member is dissolved, and the two members are bonded to produce the laminate.
- an adhesive is applied to the one surface, and the two members are bonded together through the adhesive layer to manufacture the laminate.
- the seeded cells grow and proliferate within an area having a certain thickness (for example, on the order of 100 ⁇ m) from the surface.
- a certain thickness for example, on the order of 100 ⁇ m
- the porous member of the order of 100 ⁇ m is very thin and difficult to handle, and it is difficult to laminate it on the core member by the paste method.
- the scaffold material is designed freely according to the tissue to be regenerated.
- the core member has a complicated shape, such as a tube shape and an auricular cartilage shape, it is not easy to put the porous member on the surface of the shape, and it is not a practical method. .
- the pores may disappear or be deformed.
- an adhesive layer formed by melting or dissolving any of the members is interposed between the porous member and the core member.
- the said contact bonding layer comprised with the said adhesive agent interposes between the said porous member and a core member. Such an adhesive layer is not necessary as a function of the scaffold material.
- Such a problem is not limited to the scaffold material, but also applies to biomaterials such as anti-adhesion materials and stents that are attracting attention as uses of the porous member.
- the present invention provides, for example, a porous member formed without using the paste method as described above, a method for making a polymer substrate porous for producing such a porous member, and the porous member. It aims at providing the manufacturing method of.
- the porous member of the present invention is a porous member having a porous surface, and has a core layer and a porous surface layer, and the core layer and the surface layer are made of the same polymer raw material.
- the surface layer is integrally formed on the surface of the core layer, and no adhesive layer is provided between the core layer and the surface layer.
- the porous method of the present invention is a porous method for making the surface of a polymer substrate porous, It includes the following steps (A) and (B).
- the production method of the present invention is a method for producing a porous member, characterized in that the surface of a polymer substrate is made porous by the above-described porous method of the present invention.
- the scaffold material of the present invention is manufactured by the manufacturing method of the present invention.
- the porous member of the present invention is a porous member formed without using the paste method as described above. Therefore, unlike the porous member obtained by the paste method, for example, the porous member of the present invention has an adhesive layer formed by bonding members between the core layer and the porous surface layer. It becomes a shape that does not.
- Such a porous member can be manufactured, for example, by the porous method and the manufacturing method of the present invention as described above. That is, according to the porous method and production method of the present invention, the surface of the polymer substrate can be easily made porous simply by lyophilizing the polymer substrate after immersing the polymer substrate in the solvent. . Thereby, the porous member of the present invention in which the porous surface layer is integrally formed on the surface of the core layer can be manufactured.
- a porous surface layer can be formed only by immersing in the solvent and lyophilizing the polymer substrate. . Therefore, according to the production method of the present invention, it is possible to easily form a porous member in which the porous surface layer and the core layer are integrated without being affected by the shape of the polymer substrate. is there. Thus, according to the present invention, since a porous member having a desired shape without an adhesive layer can be easily produced, the applicable range of the porous member can be further expanded. For this reason, the present invention can be said to be extremely useful, for example, in the field of regenerative medicine.
- FIG. 1 is a cross-sectional photograph of an example of a scaffold material in Example 1 of the present invention.
- FIG. 2 (A) is a graph showing the relationship between the immersion time and the thickness of the surface layer in Example 1 of the present invention, and
- FIG. 2 (B) shows the immersion time and the core layer in Example 1 described above. It is a graph which shows the relationship with thickness.
- FIG. 3 is a SEM photograph of an example of a scaffold material in Example 1 of the present invention.
- FIG. 4 is a graph showing the relationship between the freezing treatment temperature and the average pore size of the surface layer in Example 1 of the present invention.
- FIG. 5 is a graph showing the results of cell number measurement in Example 2 of the present invention.
- FIG. 6 is an external view photograph of an auricle-shaped scaffold material in Example 3 of the present invention.
- FIGS. 7A and 7B are cross-sectional photographs of the pinna-shaped scaffold material in Example 3 of the present invention.
- FIG. 8 is an example of the porous member of the present invention, in which (A) is a plan view, (B) is a sectional view, and (C) is a perspective view in use.
- FIG. 9 shows another example of the porous member of the present invention, in which (A) is a perspective view and (B) is a cross-sectional view.
- the porous member of the present invention is a porous member having a porous surface, and has a core layer and a porous surface layer, and the core layer and the surface layer are the same. It is composed of a polymer raw material, the surface layer is integrally formed on the surface of the core layer, and no adhesive layer is provided between the core layer and the surface layer. In the present invention, for example, it can be said that the surface layer is formed on the surface of the core layer without using the adhesive layer.
- the porous member of the present invention can be manufactured, for example, by a manufacturing method described later.
- the reason why such a porous member can be manufactured by the manufacturing method of the present invention is estimated as follows.
- the surface of the polymer substrate is gradually dissolved by the solvent and is swollen by the solvent, for example, in a gel form.
- the swelling region on the surface of the polymer substrate is made porous, and as a result, a porous member in which the surface of the polymer substrate is made porous is obtained.
- the core layer can be said to be a layer that maintains the physical properties of the polymer substrate, for example. Note that the present invention is not limited to this estimation.
- the porous member of the present invention has a shape that does not have an “adhesive layer” formed by bonding between the core layer and the surface.
- the “adhesive layer” is a layer formed when a core member and a porous member are separately prepared and pasted, as in the above-described paste method, for example.
- the layer (adhesive agent layer) containing the said adhesive agent is mention
- an adhesive penetrates into a layer formed between the core member and the porous member, or a hole exposed on the bonding surface of the porous member or the core member.
- Layer and the like for example, when the substrates are bonded by the heat treatment or the solvent treatment, a layer in which the core member or the porous member is dissolved or melted and solidified again can be given.
- a layer or the like formed by the dissolved polymer entering the inside of the hole exposed on the bonding surface of the porous member and solidifying, etc. can give.
- the use of the porous member of the present invention is not particularly limited, and examples thereof include a biological member used in vivo and a non-biological member used in vitro.
- the biological member include a scaffold material for cells or tissue in vivo, an adhesion prevention material, a stent, a bioprosthetic material, and the like.
- the living body to which the biological member is applied is not particularly limited, and examples thereof include animals such as humans, mammals other than humans, and birds. Examples of mammalian animals other than humans include monkeys, dogs, cats, horses, Examples include cattle, sheep, goats, pigs, mice, rats, rabbits and hamsters.
- the non-biological member include a cell or tissue scaffold material collected from a living body, a substrate such as a cell culture container, and the like.
- the size of the porous member of the present invention can be appropriately set according to the application and is not particularly limited.
- the shape of the porous member can be appropriately set according to the application, for example, and is not particularly limited. Specific examples of the shape include a film shape, a plate shape, a block shape, a columnar shape, a tubular shape, a tubular shape, a spherical shape, and a weight shape, and may be a shape obtained by combining these shapes.
- the porous member may be hollow or non-hollow, for example.
- the shape of the porous member may be, for example, the whole shape or the shape of a part of the living tissue.
- the biological tissue is not particularly limited, for example, auricle, nose, meniscus, pharynx, eyes, teeth, blood vessels, bone, cartilage, ligament, skin, breast, tail, spinal cord, brain, pancreas, liver, kidney , Heart, intestines and the like.
- the surface layer may be formed on the entire surface or a part of the surface of the core layer.
- the formation region of the surface layer can be appropriately determined according to the use of the porous member, for example.
- the surface layer is provided in a region where affinity with cells in the living body is required on the surface of the porous member.
- the thickness of the surface layer is not particularly limited, and is, for example, on the order of several tens of ⁇ m to several hundreds of ⁇ m, preferably 10 to 1000 ⁇ m, more preferably 50 to 500 ⁇ m, and still more preferably 100 ⁇ 150 ⁇ m.
- the thickness of the surface layer is preferably substantially uniform, for example. “The thickness of the surface layer is substantially uniform” means, for example, that the variation in the thickness of the surface layer is, for example, ⁇ 0% of the average thickness to ⁇ 15% of the average thickness, and preferably ⁇ of the average thickness. 0% to ⁇ 5% of average thickness. The variation includes, for example, the standard deviation of the measured thickness.
- the size and thickness of the core layer are not limited at all, and can be determined as appropriate depending on, for example, the use of the porous member and the rigidity required for the porous member.
- the thickness is preferably thicker than, for example, the surface layer. As a specific example, the thickness is, for example, 1000 ⁇ m or more.
- the pore size of the surface layer is not particularly limited, and can be appropriately determined according to the use of the porous member, for example.
- the average pore size of the surface layer is, for example, 5 to 500 ⁇ m, preferably 10 to 60 ⁇ m.
- the pore size of the surface layer may be non-uniform, for example, but is preferably uniform.
- the core layer may be porous or non-porous, for example.
- the average pore size is not particularly limited and is, for example, 1 to 10 ⁇ m.
- the average pore size of the core layer may be uniform or non-uniform, for example, and is not particularly limited.
- the porosity of the surface layer is not particularly limited and is, for example, 50 to 99%.
- the porosity is not particularly limited.
- the porosity is preferably relatively smaller than the porosity of the surface layer in order to maintain rigidity.
- the porosity is, for example, less than 50%.
- the porous member of the present invention may further include other layers.
- the other layer may be, for example, one layer or two or more layers.
- the other layer is preferably laminated with a region where the surface layer is not formed in the core layer, for example.
- the other layer and the core layer may be stacked via the adhesive layer, for example.
- the porous member of the present invention may have a drug, for example.
- the drug is not particularly limited, and examples thereof include physiologically active substances such as various growth factors, anti-infective agents, anticancer agents, anti-inflammatory agents, and analgesics.
- the scaffold material is, for example, a member that serves as a scaffold for cell or tissue proliferation.
- the scaffold material may be used, for example, in vitro or in vivo. When used in vitro, the scaffold material can grow and proliferate the cells or tissues, for example, by seeding and culturing the cells or tissues.
- the cell may be, for example, a cell collected from a living body or a cultured cell established.
- the type of the cell is not particularly limited, and examples thereof include vascular cells, chondrocytes, ⁇ cells of islets of Langerhans, skin cells, nerve cells, mesenchymal stem cells, osteoblasts, adipocytes and the like.
- the origin of the cells is not particularly limited, and examples thereof include various animals as described above.
- the scaffold material in which cells are cultured in this way may be placed in a living body after cell culture, for example.
- the scaffold material when used in vivo, is disposed in, for example, a tissue in a living body and can proliferate cells and tissues in the living body.
- the biological tissue in which the scaffold material is disposed is not particularly limited, and examples thereof include the aforementioned biological tissue.
- the kind of living body to which the scaffold material is applied is not particularly limited, and examples thereof include various animals as described above.
- the shape of the scaffold material is not particularly limited, and examples thereof include a block shape.
- the pore size of the surface layer is preferably a size that allows seeding and proliferation of cells, for example.
- the average pore size of the surface layer is, for example, 5 to 500 ⁇ m, preferably 10 to 60 ⁇ m.
- the said adhesion prevention material is a member which prevents the adhesion between the said tissues by arrange
- the shape of the adhesion preventing material is not particularly limited, and is preferably a film shape or a sheet shape.
- both surfaces of the core layer may have the porous surface layer, but it is preferable that only one surface has the surface layer.
- the adhesion preventing material may be arranged as it is on the affected part in a living body, or may be wound around the affected part when the affected part is tubular.
- a porous member shown in FIG. 8 is preferable.
- FIG. 8 is a view showing an example of the porous member of the present invention. 8A is a plan view of the porous member 1
- FIG. 8B is a cross-sectional view taken along the II direction of the porous member 1 in FIG. 8A
- FIG. 8C is the use of the porous member 1. It is a perspective view which shows the form of time.
- the porous member 1 has a core layer 11 and a porous surface layer 10, except for both end portions 11 a and 11 b of the core layer 11, without the surface layer 10 being on the surface of the core layer 11 via an adhesive layer, Is formed.
- the porous member 1 can be used as shown in FIG. That is, the porous member 1 winds the affected part so that the porous surface layer 10 contacts the tubular affected part. Then, both end portions 11a and 11b of the core layer 11 are overlapped and fused with an electric knife or the like.
- the core layer 11 is preferably non-porous rather than porous.
- the stent is a tubular device generally installed in a tubular tissue of a living body such as a blood vessel, trachea, esophagus, duodenum, bile duct, and the like. This can prevent stenosis and the like.
- the shape of the stent is preferably, for example, tubular. Since the stent is inserted into the lumen, its outer surface is in contact with the tubular tissue, and, for example, bile, blood, digest, etc. pass through the inside depending on the type of the tubular tissue. . In order to stably install the stent in a living body, for example, it is desired that the outer surface of the stent is excellent in affinity with living cells. For this reason, the stent is preferably a porous member having the porous surface layer formed on the outer surface thereof.
- porous member for example, in vivo, cells in contact with the outer surface enter the surface layer of the scaffold material and proliferate, so that the stent is stably installed. it can.
- the bile and the like pass through the inside of the stent, for example, it may not have the porous surface layer.
- the inner surface may be a non-porous surface layer. But you can.
- FIG. 9 is a diagram showing an example of the porous member of the present invention.
- 9A is a perspective view of the porous member 2
- FIG. 9B is a cross-sectional view of the porous member 2 taken along the line II-II in FIG. 9A.
- the porous member 2 has, for example, a tubular core layer 21 and a surface layer 20, and the surface layer 20 is integrated with the surface of the core layer 21 except for both end portions 21 a and 21 b of the core layer 21. .
- the porous member 2 is sutured with its tubular tissue by inserting both end portions 21a and 21b into the lumen.
- Both end portions 21a and 21b to be stitched portions are preferably nonporous rather than porous, for example, because it is desired to sew without tearing, more preferably, more than a porous surface layer, A non-porous core layer with high thread tension is preferred.
- the said prosthetic material for living bodies is a member which supplements a living body cell or a living body tissue by arrange
- Specific examples of the bioprosthetic material include an artificial bone placed in a bone defect, a bone pin for fixing the bone, and the like.
- the porous method of the present invention is a porous method for making the surface of a polymer substrate porous, It includes the following steps (A) and (B).
- the above-described porous member of the present invention can be produced.
- the porosity forming method of the present invention can also be called, for example, a method for modifying the surface of a polymer substrate.
- the size and shape of the porous member of the present invention depend on, for example, the size and shape of the polymer substrate used.
- the size and shape of the polymer substrate are not particularly limited, and can be appropriately set according to the size and shape of the desired porous member, for example.
- Examples of the shape of the polymer substrate include the shape of the porous member described above.
- the polymer substrate may be hollow or non-hollow, for example.
- the shape of the polymer substrate may be, for example, the shape of the whole or a part of the living tissue.
- the biological tissue is not particularly limited, and examples thereof include the aforementioned biological tissue.
- the polymer substrate may be porous or non-porous, for example.
- porosification refers to the number of pores that are further porous when the surface of the polymer substrate before the immersion treatment is porous, for example, the pores are made smaller or larger. It also includes the meaning of increasing.
- the polymer base material may be, for example, a single layer polymer base material or a multilayer polymer base material having two or more layers. In the latter case, for example, each layer may be composed of the same polymer raw material or may be composed of different polymer raw materials.
- the multilayer polymer substrate can be set with physical properties such as rigidity and in vivo degradation rate as desired, for example, by selecting a polymer raw material for each layer.
- the polymer material constituting the polymer substrate is not particularly limited, and various polymers can be used.
- the polymer is not particularly limited.
- the polymer is preferably, for example, a polymer exhibiting biocompatibility, or may be a biodegradable polymer that is degraded in vivo after a certain period of time.
- the polymer may be, for example, a non-biodegradable polymer.
- the molecular weight of the polymer is not particularly limited, and is, for example, 5,000 to 2,000,000, preferably 10,000 to 1,500,000, and more preferably 100,000 to 1,000. 000,000.
- the polymer may be, for example, a homopolymer or a copolymer such as a random polymer, a block polymer, or a graft polymer.
- the biodegradable polymer is not particularly limited, and examples thereof include aliphatic polyester, polyvinyl alcohol, polyethylene glycol, polycarbonate, polyamide, and the like, and preferably aliphatic polyester.
- the monomer constituting the biodegradable polymer is not particularly limited.
- Examples of the lactone include ⁇ -butyrolactone, ⁇ -valerolactone, and ⁇ -caprolactone, and ⁇ -caprolactone is preferable.
- the combination and ratio of the monomers are not particularly limited.
- the combination of the monomers include lactide and lactone, glycolide and lactone, and preferably lactide and lactone. Specific examples include lactide and ⁇ -caprolactone, glycolide and ⁇ -caprolactone, and the like. Preferred are lactide and ⁇ -caprolactone.
- the ratio of the monomer to be combined is not particularly limited.
- the molar ratio (lactide: lactone) is, for example, 90:10 to 10:90 Yes, preferably from 85:15 to 20:80, and more preferably from 80:20 to 40:60.
- the biodegradable polymer may be a natural polymer such as collagen, hyaluronic acid, elastin, chitosan, chitin, chondroitin sulfate, or cellulose.
- the natural polymer is not particularly limited, and may be, for example, an extract from a living tissue or cell, a product of a transformant, or a synthetic product.
- the natural polymer may be, for example, a product obtained by further modifying or derivatizing the extract, the product, or the synthetic product.
- the non-biodegradable polymer is not particularly limited, and examples thereof include polyethylene and polyurethane.
- the polymer raw material may be, for example, any one of the aforementioned polymers, or may include two or more types. In the latter case, the combination and ratio are not particularly limited and can be set as appropriate.
- the polymer raw material may contain other components in addition to the aforementioned polymer, for example.
- the other components are not particularly limited, and may include, for example, hydroxyapatite, titanium and the like.
- the solvent for immersing the polymer substrate is not particularly limited, and a solvent capable of dissolving the polymer substrate can be used.
- the solvent can dissolve the single-layer polymer substrate, that is, the polymer raw material constituting the single-layer polymer substrate can be dissolved. Any solvent can be used.
- the solvent is a solvent that can dissolve at least one outermost layer that makes the surface porous, that is, a solvent that can dissolve the polymer raw material constituting the outermost layer. it can.
- the solvent can be appropriately determined according to, for example, the type of the polymer raw material.
- the solvent include organic solvents such as acetone, toluene, benzene, chloroform, methyl ethyl ketone, 1,4-dioxane, dimethyl carbonate, dimethylformamide and hexafluoroisopropanol, and aqueous solvents such as water.
- the solvent may be, for example, any one kind or a mixed solvent of two or more kinds.
- the mixed solvent may be, for example, a mixed solvent of the organic solvent and the aqueous solvent.
- the combination of the solvent and the polymer raw material is not particularly limited.
- the combination include, for example, a combination of 1,4-dioxane and a lactide-caprolactone copolymer, a combination of hexafluoroisopropanol and polyglycolic acid, a combination of hexafluoroisopropanol and polyparadioxanone, and the like. It is done.
- the time for immersing the polymer substrate in the solvent is not particularly limited, and can be appropriately determined according to the combination of the polymer substrate and the solvent.
- the immersion time is, for example, 1 to 600 seconds.
- the thickness of the surface layer to be formed, the pore size of the surface layer, and the like can be controlled by adjusting the immersion time. Specifically, for example, if the immersion time is relatively long, the surface layer can be relatively thick, and the pore size can be relatively large. On the other hand, for example, when the immersion time is relatively short, the thickness of the surface layer can be relatively thin, and the pore size can be relatively small.
- the swollen region of the polymer substrate is the surface layer, and the non-swelled region is the core layer. For this reason, for example, as the thickness of the surface layer increases, the thickness of the core layer decreases.
- the temperature of the immersion treatment is not particularly limited.
- the temperature of the immersion treatment is preferably, for example, higher than the melting point of the solvent to be immersed and lower than the boiling point of the solvent.
- the temperature of the immersion treatment is, for example, in the range of 12 to 101 ° C.
- the immersion of the polymer substrate may be performed by, for example, putting the polymer substrate into a container containing the solvent. It is preferable that the polymer base material is immersed in the solvent in a state where the polymer base material does not contact the side surface and the bottom surface of the container. Thereby, for example, the porous surface layer can be formed more uniformly. Moreover, when the polymer base material is immersed in the solvent, for example, the solvent in the container may be gently stirred with a stirrer or the like.
- the whole may be immersed in the solvent, or may be partially immersed.
- the entire surface of the single-layer polymer substrate is made porous, it is preferably immersed in the solvent with the entire surface of the single-layer polymer substrate exposed.
- the desired surface of the single layer polymer is made porous, for example, only the desired surface may be immersed in the solvent, or the single layer polymer group may be exposed with only the desired surface exposed.
- the entire material may be immersed in the solvent.
- the method for exposing only the desired surface is not particularly limited, and can be performed, for example, by masking an arbitrary surface of the polymer substrate.
- the whole may be immersed in the solvent, or may be partially immersed.
- the immersion treatment can be set by making only one surface porous or making both surfaces porous.
- the multilayer polymer substrate may, for example, immerse only one outermost layer in the solvent, or expose only the surface of one outermost layer, The entire multilayer polymer substrate may be immersed in the solvent.
- both surfaces are made porous, for example, the entire multilayer polymer substrate may be immersed in the solvent.
- the entire multilayer polymer substrate may be immersed in the solvent.
- the entire multilayer polymer substrate when one outermost layer can be dissolved in the solvent and the other outermost layer does not dissolve in the solvent, for example, the entire multilayer polymer substrate may be immersed in the solvent. .
- the multilayer polymer substrate is a layer in which one outermost layer can be dissolved in the solvent, and the other outermost layer.
- the outer layer is preferably a layer that does not dissolve in the solvent.
- only the desired one surface can be easily made porous by simply immersing the whole in the solvent and from the difference in solubility of each layer in the solvent.
- the layer that is soluble in the solvent and the layer that is not soluble in the solvent can be set, for example, based on the solubility of the polymer raw material in the solvent.
- Specific examples include a layer composed of a copolymer of lactide and caprolactone (P (LA / CL)) and a layer composed of polyglycolic acid (PGA).
- a multilayer polymer substrate having these layers as the outermost layers is immersed in, for example, dioxane capable of dissolving P (LA / CL).
- dioxane capable of dissolving P (LA / CL).
- PGA does not dissolve in dioxane
- the outermost layer of P (LA / CL) is subjected to a porous treatment, and the outermost layer of PGA is not subjected to a porous treatment.
- the multilayer polymer substrate is a multilayer polymer substrate having three or more layers, the type of the intermediate layer sandwiched between the two outermost layers is not limited.
- not dissolving in the solvent includes, for example, not completely dissolving but also meaning not substantially dissolving.
- the phrase “not substantially dissolved” means, for example, that it dissolves but does not correspond to the dissolution that leads to the porosity as intended by the present invention.
- the non-porous portion of the outermost layer becomes the core layer in the porous member of the present invention described above, and the porous surface of the outermost layer is It becomes a surface layer.
- the multilayer polymer base material is used, as in the case of the single layer polymer base material, for example, by masking an arbitrary surface of the outermost layer, only the desired surface is exposed to make the surface porous. Can do.
- the film-like polymer base material is masked at positions corresponding to the end portions 11a and 11b of FIG.
- the member for masking is not limited at all, and for example, it is sufficient that the solvent does not penetrate into the masked region.
- the entire polymer substrate is immersed in the solvent with the polymer substrate masked. Thereby, the surface other than the masked region is made porous.
- This porous surface is a surface layer 10 in FIG.
- a cylindrical base material made of a material insoluble in a solvent for example, silicon
- a solvent for example, silicon
- Freeze-drying process Next, the polymer base material immersed in the solvent is freeze-dried. Freeze-drying can usually be performed by drying under reduced pressure after performing a freezing treatment.
- the freezing temperature is not particularly limited, and is, for example, ⁇ 196 to 0 ° C., preferably ⁇ 50 to 0 ° C.
- the freezing treatment temperature may be, for example, a set temperature of a freezing apparatus when the polymer substrate is frozen by cooling, or may be a temperature of the polymer substrate at the time of freezing treatment and / or completion of freezing.
- the pore size of the formed surface layer can be controlled by adjusting the freezing treatment temperature. Specifically, for example, when the freezing processing temperature is set relatively high, the pore size can be set relatively large, and when the freezing processing temperature is set relatively low, the pore size can be set relatively small. .
- the cooling of the polymer substrate may be performed, for example, under a constant temperature condition or while gradually lowering the freezing treatment temperature.
- the freezing treatment temperature may be lowered intermittently or may be lowered continuously.
- the cooling rate is not particularly limited, and is, for example, ⁇ 3 to ⁇ 1000 ° C./hour, and preferably ⁇ 3 to ⁇ 750 ° C./hour.
- the freezing completion temperature is, for example, the above-described temperature range.
- the freezing processing time from the start of cooling to the completion of freezing is not particularly limited.
- the freezing time is, for example, 0.1 to 5 hours.
- the immersed polymer base material may be frozen in a state where it is immersed in the solvent, or may be frozen after being taken out from the immersed solvent, but the former is preferable.
- the freezing treatment can be performed while maintaining the shape of the swelling region formed in the solvent on the surface of the polymer substrate. For this reason, the fall of the uniformity of the surface layer formed can be prevented further, for example.
- the means for freezing is not particularly limited, and for example, a conventionally known device such as a freezer can be used.
- the reduced-pressure drying treatment temperature is not particularly limited, and is, for example, ⁇ 50 to 90 ° C., preferably ⁇ 20 to 25 ° C.
- the reduced-pressure drying treatment temperature is, for example, a set temperature of a drying device when the polymer base material is dried under reduced pressure.
- the processing time of the reduced-pressure drying is not particularly limited, and it is sufficient that, for example, the polymer base frozen body obtained in the step (B) can reduce the solvent content, that is, the solvent is removed from the frozen body. I can do it.
- the treatment time is, for example, 0.5 to 120 hours, preferably 1.5 to 12 hours.
- the pressure for the drying under reduced pressure is not particularly limited, and is, for example, 1 to 2 Pa. In the present invention, the reduced pressure includes, for example, the meaning of vacuum.
- the drying of the frozen body may be performed, for example, under a constant temperature condition or while gradually increasing the processing temperature.
- the treatment temperature may be raised intermittently or continuously, for example.
- the temperature may be continuously increased at a constant temperature increase rate.
- the rate of temperature increase is not particularly limited, and is, for example, 1 to 150 ° C./hour, preferably 6.25 to 50 ° C./hour.
- the final processing temperature is, for example, the above-described temperature range.
- the pore size of the surface layer can be controlled by adjusting the heating rate, and a surface layer having a relatively uniform pore size can be formed.
- the drying means is not particularly limited, and for example, a conventionally known device such as a freeze dryer can be used.
- the scaffold material of the present invention as described above can be produced by immersing the polymer base material in the solvent in the step (A) and freeze-drying in the step (B).
- the production method of the present invention is a method for producing a porous member, characterized in that the surface of a polymer substrate is made porous by the above-described porous method of the present invention.
- the present invention is, for example, a method for producing a porous member having a porous surface, and includes the steps (A) and (B).
- the production method of the present invention is characterized in that the porous method of the present invention is performed, and other processes and conditions are not limited at all.
- the production method of the present invention can be referred to the above-described porous method of the present invention unless otherwise specified.
- Example 1 scaffold materials having different surface layer thicknesses were produced by changing the immersion time.
- lactide-caprolactone copolymer P (LA / CL) was prepared.
- the P (LA / CL) had a molar ratio of L-lactide after synthesis of ⁇ -caprolactone of 75.1: 24.9 and an average molecular weight (Mw) of 351,000.
- Mw average molecular weight
- a stainless steel mold having an outer diameter of 120 ⁇ m, an inner diameter of 100 ⁇ m, and a cavity depth of 1000 ⁇ m, a Teflon (registered trademark) sheet (trade name Nitoflon No. 970-2UL) and a Teflon (registered trademark) film (trade name: Nitoflon No.
- the cooling shelf temperature was 0 ° C.
- the cooling time was 3 hours
- the cooling shelf temperature was ⁇ 30 ° C. and ⁇ 50 ° C.
- the cooling time was 1 hour.
- the temperature in the freeze dryer was raised to 25 ° C. at a temperature rising rate of 25 ° C./hour and vacuum dried to obtain a scaffold material.
- a surface layer located on the upper opening side of the metal petri dish is referred to as an “upper surface layer”
- a surface layer located on the inner bottom side of the metal petri dish is designated as “ Lower surface layer ”.
- Fig. 1 shows a cross-sectional photograph of the scaffold material prepared under conditions of an immersion time of 10 seconds and a freezing treatment temperature of -50 ° C.
- a1 is an upper surface layer
- a2 is a lower surface layer
- b is a core layer.
- the thicknesses of the surface layers a1 and a2 were uniform, and the thickness of the core layer b was also uniform.
- the thicknesses of the surface layer and the core layer were uniform for the scaffold materials obtained at other immersion times and freezing treatment temperatures.
- FIG. 2A shows the relationship between the immersion time of the polymer substrate and the upper surface layer and the lower surface layer of the scaffold material
- the graph of FIG. 2B shows the immersion time
- the relationship with the thickness of the said core layer in the said scaffold material is shown.
- the horizontal axis represents immersion time (seconds)
- the vertical axis represents thickness ( ⁇ m).
- the thickness of the surface layer, the core layer, and the scaffold material can be adjusted by the immersion time in the solvent.
- FIG. 3 shows an SEM photograph of the scaffold material prepared under conditions of an immersion time of 10 seconds and a freezing temperature of ⁇ 50 ° C.
- FIG. 3 is a photograph of the upper surface layer in the scaffold material.
- the length of the bar shown at the lower right of the photograph corresponds to 100 ⁇ m.
- the scaffold material had a uniform pore size in the upper surface layer. Even in the lower surface layer of the scaffold material, it was confirmed that the pore size was uniform.
- the scaffold materials obtained at other immersion times and freezing treatment temperatures have uniform pore sizes in the respective surface layers.
- the horizontal axis represents the freezing temperature (° C.)
- the vertical axis represents the average pore size ( ⁇ m) of the upper surface layer.
- the average pore size increased as the freezing treatment temperature increased. From this result, it was found that, for example, the pore size can be adjusted by the freezing treatment temperature.
- Example 2 In this example, cells were seeded on the scaffold material and cultured until 18 days after the start of the culture, and the proliferation was confirmed.
- a scaffold material was produced in the same manner as in Example 1 except that the immersion time of the polymer substrate was 10 seconds and the freezing treatment temperature was ⁇ 50 ° C.
- the scaffold material was cut to a size of 5 mm ⁇ 5 mm, immersed in 99.5 v / v% ethanol overnight, and then dried.
- Cell seeding Chinese hamster lung-derived fibroblasts (V79) were added to a MEM medium containing 10% fetal bovine serum (FBS) so as to be about 7.7 ⁇ 10 5 cells / mL to prepare a cell suspension. .
- the dried scaffold material was placed in a 30 mL syringe and filled with 10 mL of the cell suspension.
- a one-way valve was attached to the tip of the syringe, the plunger was pulled to decompress the inside of the syringe, and the air in the scaffold material was removed.
- the syringe was lightly tapped to remove air in the syringe.
- This air removal operation was repeated three times, and 10 mL of the cell suspension was further replaced, and the air removal operation was repeated three times in the same manner as described above.
- the scaffold material impregnated with the cell suspension and a MEM medium containing 10 v / v% FBS were placed in a culture flask and cultured for 18 days. The culture was stationary culture for the first day and shaking culture for the remaining period. Medium exchange at the time of culture was performed on the cell growth evaluation day described later.
- cell proliferation was evaluated after 1, 4, 8, 11, 15 and 18 days from the start of culture as follows. That is, first, the scaffold material was gently washed with a phosphate buffer solution (PBS). Next, the scaffold material was immersed in 1 mL of 0.05 w / v% trypsin and treated at 37 ° C. for 30 minutes to detach the cells from the scaffold material. The obtained exfoliated cell solution was added to 9 mL of an electrolytic solution (trade name Isoton, manufactured by Beckman Coulter, Inc.), and the number of cells was counted using a Coulter counter. The count was for suspended matter of 10 ⁇ m or more.
- PBS phosphate buffer solution
- the graph of FIG. 5 shows the measurement results of the cell number.
- the horizontal axis represents the number of days (days) from the start of culture, and the vertical axis represents the number of cells ( ⁇ 10 4 cells).
- the number of cells increased with the number of culture days. From this result, the proliferation of the cells seeded on the scaffold material was confirmed.
- the scaffold material was Giemsa stained. As a result, staining was confirmed on the surface layer of the scaffold material, and the staining became darker with time according to the number of days of culture, so that it was confirmed that cells were proliferating in the surface layer.
- Example 3 In this example, an auricle-shaped scaffold material was produced.
- Example 1 The P (LA / CL) of Example 1 was heated to 200 ° C. and injected into a silicon mold having an auricle-shaped cavity. The silicon mold was immersed in ice water, and the P (LA / CL) was cured by cooling. The cured P (LA / CL) was taken out of the silicon mold and used as a pinna-shaped polymer substrate.
- a scaffold material was prepared in the same manner as in Example 1 except that the immersion time of the polymer substrate was 1 to 2 seconds and the temperature of the cooling shelf (freezing treatment temperature) was ⁇ 80 ° C.
- the shape of the obtained scaffold material was observed. Further, the scaffold material was cut using a microtome blade, and a cross section thereof was photographed with a digital microscope (VHX-900, manufactured by Keyence Corporation).
- FIG. 6 shows a photograph of the appearance of the scaffold material
- FIG. 7 shows a cross-sectional photograph of the scaffold material
- 7A is a photograph of a part of the cross section in the II direction in FIG. 6
- FIG. 7B is a photograph of a part of the cross section of another part.
- the obtained scaffold material had a complicated auricular structure such as an ankle ring, a scaphoid fossa, an auricular concha, and an auricle, and was formed in substantially the same shape as the polymer base material.
- the scaffold material has a complicated shape having various curved surfaces in which a porous surface layer (for example, a layer indicated by an arrow in FIG. 7B) is formed on the entire surface. Nevertheless, the thickness of the surface layer was almost uniform.
- the manufacturing method of the present invention could easily form a scaffold material having a complicated shape without forming an adhesive layer.
- the porous member of the present invention is a porous member formed without using the paste method as described above. For this reason, the porous member of the present invention is different from the porous member obtained by the paste method, for example, and does not have an adhesive layer formed by bonding the member between the core layer and the porous surface layer. It becomes.
- Such a porous member can be produced, for example, by the method for producing a porous member of the present invention as described above. That is, according to the production method of the present invention, the surface of the polymer substrate can be easily made porous simply by lyophilizing the polymer substrate after immersing the polymer substrate in the solvent. Thereby, the porous member of the present invention in which the porous surface layer is integrally formed on the surface of the core layer can be manufactured.
- the production method of the present invention it is possible to easily form a scaffold material in which the porous surface layer and the core layer are integrated without being affected by the shape of the polymer substrate.
- the present invention since a porous member having a desired shape without an adhesive layer can be easily provided, the present invention is extremely useful for providing scaffold materials and the like in the field of regenerative medicine, for example. It can be said that it is useful.
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Abstract
Description
下記(A)工程および(B)工程を含むことを特徴とする。
(A)前記ポリマー基材を、前記ポリマー基材を溶解可能な溶媒に浸漬する浸漬工程
(B)前記浸漬後のポリマー基材を、凍結乾燥する凍結乾燥工程
本発明の多孔性部材は、前述のように、多孔性の表面を有する多孔性部材であって、コア層と多孔性の表面層とを有し、前記コア層と前記表面層とは、同じポリマー原料で構成され、前記コア層の表面に、前記表面層が一体化して形成され、前記コア層と前記表面層との間に、接着層を有していないことを特徴とする。本発明は、例えば、前記接着層を介することなく、前記コア層の表面に、前記表面層が形成されているということもできる。
前記足場材料は、例えば、細胞または組織の増殖の足場となる部材である。前記足場材料は、例えば、in vitroで用いてもよいし、in vivoで用いてもよい。前記in vitroで用いる場合、前記足場材料は、例えば、細胞または組織を播種して培養することにより、前記細胞または組織を生育および増殖可能である。前記細胞は、例えば、生体から採取した細胞でもよいし、株化された培養細胞でもよい。前記細胞の種類は、特に制限されず、例えば、血管細胞、軟骨細胞、ランゲルハンス島のβ細胞、皮膚細胞、神経細胞、間葉系幹細胞、骨芽細胞、脂肪細胞等があげられる。前記細胞の由来は、特に制限されず、例えば、前述のような各種動物があげられる。このように細胞を培養した前記足場材料は、例えば、細胞培養後、生体内に配置してもよい。一方、前記in vivoで用いる場合、前記足場材料は、例えば、生体内の組織に配置され、生体内の細胞および組織を増殖可能である。前記足場材料を配置する生体組織は、特に制限されず、例えば、前述の生体組織等があげられる。また、前記足場材料を適用する生体の種類も特に制限されず、前述のような、各種動物等があげられる。
前記癒着防止材は、例えば、生体内において、組織と組織との間に配置することで、前記組織間の癒着を防止する部材である。
前記ステントは、一般に、血管、気管、食道、十二指腸、胆管等の生体の管状組織に設置する管状デバイスであり、例えば、前記管状組織の管腔内部に挿入することで、吻合が原因となる狭窄等を防止できる。
前記生体用補綴材は、例えば、生体内の欠損部に配置することで、生体内細胞または生体内組織を補填する部材である。前記生体用補綴材の具体例は、例えば、骨の欠損部に配置する人工骨、骨を固定するための骨ピン等があげられる。
本発明の多孔化方法は、ポリマー基材の表面を多孔化する多孔化方法であって、
下記(A)工程および(B)工程を含むことを特徴とする。
(A)前記ポリマー基材を、前記ポリマー基材を溶解可能な溶媒に浸漬する浸漬工程
(B)前記浸漬後のポリマー基材を、凍結乾燥する凍結乾燥工程
本発明の多孔性部材の大きさおよび形状は、例えば、使用する前記ポリマー基材の大きさおよび形状に依存する。前記ポリマー基材の大きさおよび形状は、特に制限されず、例えば、所望の多孔性部材の大きさおよび形状に応じて適宜設定できる。前記ポリマー基材の形状は、例えば、前述した多孔性部材の形状等があげられる。前記ポリマー基材の形状は、例えば、中空でもよいし、非中空でもよい。また、前記ポリマー基材の形状は、例えば、生体組織の全体または部分の形状でもよい。前記生体組織は、特に制限されず、例えば、前述の生体組織等があげられる。
つぎに、前記溶媒に浸漬した前記ポリマー基材を、凍結乾燥する。凍結乾燥は、通常、凍結処理を行った後に、減圧乾燥することで行える。
本発明の製造方法は、前記本発明の多孔化方法により、ポリマー基材の表面を多孔化することを特徴とする、多孔性部材の製造方法である。具体的に、本発明は、例えば、表面が多孔化された多孔性部材の製造方法であって、前記(A)工程および(B)工程を含む。
(A)前記ポリマー基材を、前記ポリマー基材を溶解可能な溶媒に浸漬する浸漬工程
(B)前記浸漬後のポリマー基材を、凍結乾燥する凍結乾燥工程
本例では、浸漬時間を変化させて、表面層の厚みの異なる足場材料を作製した。
まず、ラクチド-カプロラクトン共重合体P(LA/CL)を準備した。前記P(LA/CL)は、合成後のL-ラクチドとε-カプロラクトンとのモル比が75.1:24.9であり、平均分子量(Mw)が351,000であった。外径120μm、内径100μm、キャビティ深さ1000μmのステンレス金型の内部に、テフロン(登録商標)シート(商品名ニトフロンNo.970-2UL)およびテフロン(登録商標)フィルム(商品名ニトフロンNo.900UL)をこの順序に置き、この上に、前記P(LA/CL)パウダーを均一に置いた。そして、前記パウダー上に、前述と同じ種類のテフロン(登録商標)フィルムおよびテフロン(登録商標)シートをこの順で積層し、この上に、さらに上板を置いた。前記上板の上にプレス板を配置した。そして、前記金型内部の前記パウダーを、170℃、0.5MPaで5分間プレスした後、前記プレス板を上下に1回ずつ動かし(各1秒)、脱泡した。さらに、170℃、10MPaで5分間プレスした後、プレスした状態で、前記金型ごと40℃まで水冷した。得られた厚み1000μmのポリマー成型体を、10mm×20mmの大きさに切断して、ポリマー基材として使用した。
金属シャーレ(直径5cm)に、1,4-ジオキサン(和光純薬工業社製)約50mLを注ぎ、この中に、前記ポリマー基材を、所定時間(2、10、60、120、180、300および600秒)浸漬した。浸漬後、前記ポリマー基材を浸漬した状態のまま、前記金属シャーレを、凍結乾燥機内の所定温度に設定した冷却棚に配置し、冷却して、前記ポリマー基材を凍結した。前記冷却棚の温度を凍結処理温度とし、一定の所定温度(0℃、-30℃および-50℃)に設定した。前記冷却棚の温度が0℃の場合、前記冷却時間は3時間、前記冷却棚の温度が-30℃および-50℃の場合、前記冷却時間は1時間とした。前記凍結後、前記凍結乾燥機内の温度を、25℃/時間の昇温速度で25℃まで昇温して真空乾燥し、足場材料を得た。前記金属シャーレ内での処理により得られた前記足場材料は、前記金属シャーレの上部開口側に位置する表面層を「上側表面層」とし、前記金属シャーレの内部底面側に位置する表面層を「下側表面層」とした。
(1)外観
得られた前記各足場材料を、ミクロトーム刃を用いて厚み方向に切断し、その断面を、デジタルマイクロスコープ(VHX-900、キーエンス社製)で撮影した。
前記各足場材料の断面写真から、コア層および表面層の厚みを測定した。コア層bは、切片あたり10点で厚みを測定し(n=2)、表面層は、上側表面層a1および下側表面層a2について、それぞれ、切片あたり5点で厚みを測定し(n=4)、それぞれの平均厚みを算出した。
得られた前記各足場材料を、前述と同様に厚み方向に切断した。そして、各切片に、イオンスパッター(E-1010、日立製作所製)を用いて白金蒸着した。この蒸着切片について、前記上側表面層(a1)の表面を、SEM(Type-N、日立製作所製)を用いて撮影した。
前記(3)で得られた画像を、画像解析ソフト(Image J)を用いて解析し、前記平均ポアサイズを算出した。
本例では、足場材料に細胞を播種して、培養開始18日後まで培養し、その増殖を確認した。
前記ポリマー基材の浸漬時間を10秒とし、凍結処理温度を-50℃とした以外は、前記実施例1と同様にして、足場材料を作製した。この足場材料を、5mm×5mmの大きさに切断し、99.5v/v%エタノールに一晩浸漬した後、乾燥させた。
まず、10%ウシ胎児血清(FBS)含有MEM培地に、チャイニーズハムスター肺由来線維芽細胞(V79)を約7.7×105細胞/mLとなるように添加し、細胞懸濁液を調製した。30mLシリンジに、乾燥させた前記足場材料を入れ、前記細胞懸濁液10mLを満たした。前記シリンジの先端に一方弁を取り付け、プランジャーを引いて前記シリンジ内を減圧し、前記足場材料内の空気を除去した。前記シリンジを軽くタッピングし、シリンジ内の空気を除去した。この空気除去操作を3回繰り返し、さらに細胞懸濁液10mLを取り替えて、前述と同様にして、空気除去操作を3回繰り返した。前記細胞懸濁液を含浸させた前記足場材料と、10v/v%FBS含有MEM培地とを、培養フラスコに入れ、18日間培養した。前記培養は、はじめの1日間を静置培養とし、残りの期間を振とう培養とした。培養時における、培地交換は、後述する細胞増殖評価日に行った。
前記足場材料(n=10)について、以下のようにして、培養開始1、4、8、11、15および18日後に細胞増殖を評価した。すなわち、まず、前記足場材料をリン酸緩衝溶液(PBS)で軽く洗浄した。つぎに、前記足場材料を0.05w/v% トリプシン1mLに浸漬して、37℃で30分間処理し、前記足場材料から細胞を剥離した。得られた剥離細胞液を、電解液(商品名アイソトン、ベックマン・コールター社製)9mLに添加し、コールターカウンターを用いて、細胞数をカウントした。前記カウントは、10μm以上の浮遊物質を対象とした。
本例では、耳介形状の足場材料を作製した。
前記実施例1の前記P(LA/CL)を200℃に加温し、耳介形状の空洞を有するシリコン型の内部に注入した。前記シリコン型を氷水中に浸漬し、冷却により前記P(LA/CL)を硬化させた。硬化した前記P(LA/CL)を前記シリコン型から取り出し、耳介形状のポリマー基材とした。
前記ポリマー基材の浸漬時間を1~2秒とし、冷却棚の温度(凍結処理温度)を-80℃とした以外は、前記実施例1と同様にして、足場材料を作製した。
得られた足場材料の形状を観察した。また、前記足場材料を、ミクロトーム刃を用いて切断し、その断面を、デジタルマイクロスコープ(VHX-900、キーエンス社製)で撮影した。
Claims (25)
- 多孔性の表面を有する多孔性部材であって、
コア層と多孔性の表面層とを有し、
前記コア層と前記表面層とは、同じポリマー原料で構成され、
前記コア層の表面に、前記表面層が一体化して形成され、
前記コア層と前記表面層との間に、接着層を有していないことを特徴とする多孔性部材。 - 前記表面層の厚みが、10~1000μmである、請求項1記載の多孔性部材。
- 前記コア層が、非多孔性である、請求項1記載の多孔性部材。
- 前記コア層が、多孔性であり、前記コア層の気孔率が、前記表面層の気孔率よりも相対的に小さい、請求項1記載の多孔性部材。
- 前記ポリマー原料が、生分解性ポリマーを含む、請求項1記載の多孔性部材。
- 前記生分解性ポリマーが、ラクチドとカプロラクトンとの共重合体である、請求項5記載の多孔性部材。
- 前記多孔性部材の形状が、プレート状、柱状または管状である、請求項1記載の多孔性部材。
- 前記多孔性部材の形状が、生体組織の全体または部分の形状である、請求項1記載の多孔性部材。
- 前記多孔性部材の用途が、生体用部材である、請求項1記載の多孔性部材。
- 前記多孔性部材の用途が、細胞の足場材料、ステントまたは癒着防止材である、請求項1記載の多孔性部材。
- 前記多孔性部材の用途が、生体用補綴材である、請求項1記載の多孔性部材。
- ポリマー基材の表面を多孔化する多孔化方法であって、
下記(A)工程および(B)工程を含むことを特徴とする多孔化方法。
(A)前記ポリマー基材を、前記ポリマー基材を溶解可能な溶媒に浸漬する浸漬工程
(B)前記浸漬後のポリマー基材を、凍結乾燥する凍結乾燥工程 - 前記(B)工程において、前記ポリマー基材を、前記溶媒に浸漬した状態で、凍結する、請求項12記載の多孔化方法。
- 前記ポリマー基材を構成するポリマー原料が、生分解性ポリマーを含む、請求項12記載の多孔化方法。
- 前記生分解性ポリマーが、ラクチドとカプロラクトンとの共重合体である、請求項14記載の多孔化方法。
- 前記溶媒が、1,4-ジオキサンを含む溶媒である、請求項12記載の多孔化方法。
- 前記(A)工程において、前記ポリマー基材を前記溶媒に浸漬する時間の調節によって、形成される前記表面層のポアサイズを制御する、請求項12記載の多孔化方法。
- 前記(B)工程において、前記ポリマー基材の凍結処理温度の調節によって、形成される前記表面層のポアサイズを制御する、請求項12記載の多孔化方法。
- 前記(A)工程において、前記ポリマー基材を前記溶媒に浸漬する時間の調節によって、形成される前記表面層の厚みを制御する、請求項12記載の多孔化方法。
- 前記(B)工程において、前記ポリマー基材を一定速度で冷却する、請求項12記載の多孔化方法。
- 前記ポリマー基材が、非多孔性の基材である、請求項12記載の多孔化方法。
- 前記ポリマー基材の形状が、プレート状、柱状または管状である、請求項12記載の多孔化方法。
- 前記ポリマー基材の形状が、生体組織の全体または部分の形状である、請求項12記載の多孔化方法。
- 請求項12記載の多孔化方法により、ポリマー基材の表面を多孔化することを特徴とする多孔性部材の製造方法。
- 請求項24記載の製造方法により製造される多孔性部材。
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KR101471928B1 (ko) * | 2012-04-06 | 2014-12-12 | 포항공과대학교 산학협력단 | 세포 배양용 용기 |
JP6124845B2 (ja) | 2014-06-30 | 2017-05-10 | 三菱製紙株式会社 | 細胞又は組織のガラス化凍結保存用治具 |
CN106795475B (zh) | 2014-10-23 | 2021-01-29 | 三菱制纸株式会社 | 细胞或组织的冷冻保存用夹具及冷冻保存方法 |
CN105902331A (zh) * | 2016-04-08 | 2016-08-31 | 南京永明医疗器械有限公司 | 一种血管支架及其制备方法 |
CN109803692A (zh) | 2016-09-30 | 2019-05-24 | 株式会社Gc | 生物可吸收膜的制造方法及生物可吸收膜 |
CN108134047B (zh) * | 2016-12-01 | 2020-11-24 | 中国科学院大连化学物理研究所 | 高担量活性物质电极制备及其电极和应用 |
KR101965434B1 (ko) * | 2017-03-15 | 2019-04-03 | 주식회사 메피온 | 유착 방지재 및 그 제조 방법과 장치 |
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- 2010-12-08 WO PCT/JP2010/072009 patent/WO2011071074A1/ja active Application Filing
- 2010-12-08 EP EP20100835994 patent/EP2495303A1/en not_active Withdrawn
- 2010-12-08 JP JP2010273428A patent/JP2011139898A/ja active Pending
- 2010-12-08 KR KR1020127013998A patent/KR20120088786A/ko not_active Application Discontinuation
- 2010-12-08 CN CN2010800525137A patent/CN102753677A/zh active Pending
- 2010-12-08 US US13/513,991 patent/US20120251752A1/en not_active Abandoned
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US20120251752A1 (en) | 2012-10-04 |
EP2495303A1 (en) | 2012-09-05 |
CN102753677A (zh) | 2012-10-24 |
JP2011139898A (ja) | 2011-07-21 |
KR20120088786A (ko) | 2012-08-08 |
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