WO2002039930A1 - Film a usage medical et procede de production de celui-ci, cornee artificielle faisant appel a ce film et procede de production de celle-ci - Google Patents

Film a usage medical et procede de production de celui-ci, cornee artificielle faisant appel a ce film et procede de production de celle-ci Download PDF

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Publication number
WO2002039930A1
WO2002039930A1 PCT/JP2001/000917 JP0100917W WO0239930A1 WO 2002039930 A1 WO2002039930 A1 WO 2002039930A1 JP 0100917 W JP0100917 W JP 0100917W WO 0239930 A1 WO0239930 A1 WO 0239930A1
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WIPO (PCT)
Prior art keywords
membrane
porous layer
artificial cornea
medical
pore
Prior art date
Application number
PCT/JP2001/000917
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English (en)
Japanese (ja)
Inventor
Motonari Watanabe
Ichiro Ando
Original Assignee
Menicon Co., Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Menicon Co., Ltd. filed Critical Menicon Co., Ltd.
Priority to JP2002542307A priority Critical patent/JPWO2002039930A1/ja
Priority to AU2001232260A priority patent/AU2001232260A1/en
Publication of WO2002039930A1 publication Critical patent/WO2002039930A1/fr

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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
    • 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
    • A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix

Definitions

  • the present invention relates to a medical membrane and a method for manufacturing the same. Further, the present invention relates to an artificial cornea for replacing a cornea whose function has been reduced or lost due to an eye tissue disease or the like, and restoring visual function, The present invention relates to an artificial cornea and a method for producing the same, wherein the medical film is used as a support for surrounding and supporting at least a part of an optical part of the artificial cornea. Background art
  • an artificial cornea is provided with an optical part made of a transparent (translucent) material and a fixing part for supporting the optical part by fixing the optical part to eye tissue of a human body. It is composed of As such an artificial cornea, the present inventors have already consisted of an optical part which is a transparent (translucent) material and a support part surrounding the optical part. In addition, an artificial cornea made of a flexible material in which the supporting portion has a fine interstitial structure has been proposed (Japanese Patent Application Laid-Open No. 91-182762).
  • the present inventors have proposed an artificial corneal prosthesis in which, when the corneal prosthesis is implanted, a collar portion protruding radially outward is provided on a support portion on the side in contact with the inside of the eye. (International Publication No. WO98 / 20813).
  • the supporting portion of the artificial cornea has been made of a porous material such as a nonwoven fabric or a sponge, and a tissue invades the supporting portion.
  • the transplanted artificial cornea It is used to be more firmly fixed.
  • the general method of fixing the supporting membrane to the artificial corneal body is as follows: a) A fixing method such as a clip; b) The optical part is placed in the hole of the supporting part (sbonge). Fixing method that allows polymer to penetrate, c) Fixing method by dissolving both joining surfaces with a solvent in which the material of the support and optics are both soluble, d) —General This is a fixing method using a typical adhesive.
  • the fixing part is easily detached and the durability is problematic.
  • the fixing method in b It is difficult to control the degree of penetration of the optical member polymer into the hole of the support, and the penetration of the support blocks the tissue penetration hole of the support.
  • the fixing method of c the material of the supporting portion is dissolved by the soluble solvent and the pores are closed.
  • the fixing method d) has a problem that the adhesive closes the hole.
  • Japanese Patent Publication No. 4-158859 / 1991 discloses an artificial cornea using a porous fluorine resin as a support. Adhesion to the support and the artificial corneal body is performed by bonding with an adhesive, or the configuration of the optical unit in the mode where the support is installed in advance. At the same time when the raw material monomer is polymerized and molded, a method of bonding the optical part and the support part is described. However, as described above, the hole of the support part is closed. There is a drawback.
  • the conventional corneal prosthesis support portion has the above-mentioned eye contact. Due to the use of porous materials, the potential for infection by bacteria, viruses, etc., from external forces, may occur in some cases. Can not be denied.
  • the present invention has been made in view of the prior art, and provides a medical film and a method for manufacturing the same, which can be bonded to a device substrate while maintaining a porous structure.
  • the purpose is to do so.
  • the present invention relates to the manufacture of artificial corneas and their manufacture having a support where the porous structure for tissue penetration is retained without being destroyed during assembly.
  • the aim is to provide a method.
  • the present invention also provides a non-porous layer that can prevent the invasion or infection of bacteria, viruses, etc. from the outside, and a porous layer that can invade tissues.
  • An object of the present invention is to provide a medical membrane having a layer, an artificial cornea using the medical membrane, and a method for producing the same. Disclosure of the invention
  • the present invention relates to a medical membrane in which two or more porous layers and two or more non-porous layers are laminated.
  • the present invention relates to the medical membrane, wherein a non-porous layer is present on at least one surface of the membrane.
  • the present invention relates to a medical membrane in which each layer of the membrane is made of the same flexible material.
  • the present invention also relates to the present invention.
  • the present invention relates to a method for producing the medical film, comprising:
  • the present invention is a.
  • the present invention relates to a method for producing the medical film, comprising:
  • the present invention relates to the method for producing the medical membrane, wherein the pore-forming agent is a salt.
  • the present invention relates to a method for producing the medical membrane, wherein the ratio of the pore-forming agent to the total weight of the membrane material and the pore-forming agent is 95% by weight or less.
  • the present invention is a.
  • the present invention also relates to an artificial corneal membrane comprising the medical membrane.
  • the present invention relates to a membrane for a support portion of an artificial cornea, comprising the medical membrane.
  • the present invention is a.
  • the support part is formed by an artificial cornea consisting of the support part film.
  • the present invention relates to the artificial cornea, wherein a surface of the non-porous layer of the support portion is used as a contact surface with a main body.
  • the collar portion protrudes outward from the side surface of the optical portion so that the rear surface and the rear surface of the optical portion are flush with each other, and at least the side surface of the optical portion is provided.
  • the non-porous layer surface of the supporting portion surrounding a part relates to the human cornea, which is joined to the front surface of the collar portion.
  • the present invention relates to the artificial cornea having a protruding portion in which the hub portion protrudes outward from a supporting portion.
  • the present invention relates to the artificial cornea, wherein a hole extending from a rear surface of the collar portion to a porous layer of a support portion is provided.
  • the present invention is a.
  • An artificial cornea made of an optically transparent material, having an optical part having a front surface, a rear surface, and side surfaces, and a hub part protruding outward from a side surface of the optical part.
  • FIG. 1 is a scanning micrograph of a two-layer film composed of a porous layer 2 and a non-porous layer 3 produced by the salt extraction method in Example 1.
  • FIG. 2 is a scanning micrograph of a two-layer film composed of a porous layer 2 and a non-porous layer 3 produced by a freeze-drying method in Example 3.
  • FIG. 3 is a scanning micrograph of a three-layer film composed of the non-porous layer 3aZ porous layer 2 / non-porous layer 3b produced by the salt extraction method in Example 4. is there .
  • FIG. 4 is a schematic cross-sectional view showing one embodiment of the artificial cornea of the present invention.
  • FIGS. 5 (a) and 5 (b) are schematic plan views of the artificial cornea 4 of FIG. 4, respectively.
  • FIG. 5 (a) is a view from the front side of the artificial cornea 4 (above the schematic sectional view).
  • FIG. 5 (b) is a view from the back side of the artificial cornea 4 (the lower side of the schematic cross-sectional view).
  • FIG. 6 is a scanning micrograph of a bonding portion between the support portion 6 and the collar portion of the artificial cornea prepared in Example 5.
  • FIG. 7 (a) and 7 (b) are schematic views showing one embodiment of the artificial cornea of the present invention.
  • FIG. 7 (a) is a schematic sectional view
  • FIG. 7 (b) is a schematic plan view seen from the back side of the artificial cornea 4 of FIG. 7 (a).
  • FIG. 8 is a schematic cross-sectional view of one embodiment showing a transplantation state of a full-thickness transplant in which all layers of the cornea are replaced with the artificial cornea of the present invention.
  • FIG. 9 (a) is a tissue-stained photograph of a partial cross section of the cornea 10 of a Japanese white rabbit transplanted with the artificial cornea 4 of the present invention, and shows the artificial cornea 4 and the rabbit cornea. 10 shows the state of the interface.
  • Fig. 9 (b) is a sketch drawing for explaining the tissue staining photograph of Fig. 9 (a). is there .
  • Best Mode for Carrying Out the Invention The medical film of the present invention is a film in which two or more porous layers and non-porous layers are laminated as described above. However, a membrane having a non-porous layer at least on one surface is preferred.
  • the medical membrane of the present invention has at least one porous layer and at least one non-porous layer, respectively, even if the total number of layers is two or three or more. Okay.
  • the pore size of the pores of the porous layer of the medical membrane according to the present invention can be appropriately set according to the purpose of the present invention, but is preferably a size suitable for invasion of cell tissue. No. Specifically, it is 1 to 500 / m, preferably 5 to 200 ⁇ , and more preferably 10 to 150.
  • the porosity of the porous layer is not particularly limited as long as the purpose of the present invention can be achieved.
  • the medical membranes used in the present invention include artificial corneal membranes, skin coating membranes, artificial vascular materials, and medical membranes such as drug supply membranes and transdermal drug supply membranes. It is necessary to get a touch.
  • the material of the medical membrane of the present invention is preferably one that is excellent in biocompatibility, and can achieve the purpose of the present invention. As far as they are concerned, they are not particularly limited.
  • Examples of the above-mentioned materials include bio-derived polymers represented by various synthetic polymers and collagens; and biodegradable polymers represented by polylactic acid. Molecules, etc. are exposed.
  • each of the porous layer and the non-porous layer can be prepared by selecting each of the above-mentioned materials. It is preferred that the layers are made of the same flexible material.
  • One method for producing a medical membrane according to the present invention comprises, for example, a step of mixing a solution (A) in which the membrane material is dissolved in a solvent 1 and a pore-forming agent, and (b) A step of precipitating the pore-forming agent in the solution (A); (c) a step of evaporating the solvent 1; and (c) a step of dissolving the pore-forming agent in the solvent 2.
  • This is a method consisting of a process of producing (hereinafter, referred to as a pore forming agent addition extraction method).
  • a solution (A) in which the membrane material is dissolved in solvent 1 and a pore-forming agent insoluble in solvent 1 are mixed.
  • the mixed solution is cast after stirring, and is allowed to stand until the pore-forming agent precipitates in the solution.
  • the solvent 1 is vaporized to obtain a mixture of the membrane material and the pore-forming agent.
  • the mixture has a two-layer structure consisting of a lower layer in which the membrane material and the pore-forming agent coexist and an upper layer consisting only of the membrane material.
  • the pore-forming agent is extracted from this mixture using a solvent 2 in which the pore-forming agent is soluble and the membrane material is insoluble.
  • the pore-forming agent organic compounds such as salts, saccharides, and macromolecules are used, and among them, the point force is that it is inexpensive and easy to form into particles. It is preferable to use salt.
  • the method of using a salt as the pore-forming agent is hereinafter referred to as a salt-addition extraction method among the pore-forming agent addition extraction methods.
  • the weight ratio of salt to the total weight of the membrane material and salt is such that a non-porous layer is formed in the upper layer of the membrane, and the salt layer is formed in the lower layer.
  • the porous layer is formed by extracting As formed, it is 10-95% by weight, preferably 50-90% by weight, more preferably 60-85% by weight.
  • the salt ratio is 10% by weight or less, the proportion of the porous layer portion in the membrane tends to decrease, and when the salt ratio is higher than 95% by weight, a non-porous layer is formed. There is a tendency not to be.
  • Solvent 1 used in the salt addition extraction method of the present invention can be used for any solvent in which the membrane material to be used is soluble and the salt is insoluble.
  • the membrane material is polyurethane and the salt is sodium chloride, tetrahydrofuran, 1,4-dioxane, ⁇ , ⁇ — Dimethylform amide and ,, ⁇ — dimethylacetamide, etc. can be used.
  • the concentration of the membrane material solution ( ⁇ ) is 0.5 to 20% by weight, preferably 1 to 10% by weight, and more preferably 1 to 10% by weight. 5 to 7.0% by weight.
  • the solvent 2 used in the salt extraction method of the present invention may be any solvent in which the membrane material is insoluble and the salt is soluble.
  • the solvent in particular, things like water, methanol and glycerin are identified.
  • the salt used in the salt extraction method of the present invention is one that is insoluble in the solvent 1 that dissolves the membrane material and can be dissolved in the solvent 2 that extracts the salt.
  • Examples include, but are not limited to, alkali metal salts and alkaline earth metal salts, such as lithium chloride, beryllium chloride, and sodium chloride.
  • Hydrochlorides such as trium, magnesium chloride, potassium chloride, calcium chloride, cesium chloride, nordium chloride; lithium sulfate, sulfuric acid Sulfates such as beryllium, sodium sulfate, magnesium sulfate, potassium sulfate, calcium sulfate, cesium sulfate, barium sulfate; Or sodium hydrogen sulfate Hydrogen sulfate; lithium carbonate, sodium carbonate, magnesium carbonate, potassium carbonate, calcium carbonate, cesium carbonate, barium carbonate, etc.
  • Carbonates such as: sodium bicarbonate, sodium bicarbonate, etc .; sodium bicarbonate; sodium phosphate, magnesium phosphate, potassium phosphate Phosphates such as lime, calcium phosphate, nordium phosphate; sodium borate, potassium borate, calcium borate Borates such as um and barium borate are available.
  • salts other than the above-mentioned alkaline metals and alkaline earth metals such as aluminum sulfate, ammonium chloride, ammonium sulfate, etc., may be used. No. They may also be used in the form of hydrates.
  • the particle size is :! 5500 ⁇ , preferably 5 2200 zm, more preferably 10 ⁇ : 150 / ⁇ .
  • the purpose of the present invention is to be used.
  • the production conditions can be appropriately changed depending on the properties of the pore-forming agent to be used.
  • Another method for producing a medical membrane according to the present invention is as follows: (a) a nonporous solution prepared by previously preparing a solution (B) obtained by dissolving a membrane material in a solvent 3; (B) freezing the solution while the nonporous membrane surface is dissolved or swollen in the solution (B), and removing the solvent 3 under reduced pressure.
  • This method (hereinafter referred to as freeze-drying method) is used.
  • a nonporous membrane is prepared by casting a membrane material solution and evaporating a solvent (cast method).
  • a membrane material solution (B) in which the membrane material is dissolved in a solvent 3 is cast.
  • the surface of the non-porous membrane Is dissolved or swollen in the membrane material solution (B), and is frozen below the freezing point of the solution (B).
  • a membrane having a two-layer structure in which a porous layer and a non-porous layer are integrated by freeze-drying can be obtained. (See Figure 2).
  • a nonporous film can be produced by a compression molding method, a spray molding method, a cutting molding method, or the like.
  • the concentration of the membrane material solution (B) is 0.5 to 20% by weight, preferably; 110% by weight, more preferably 1.5-7% by weight.
  • the solvent 3 used in the freeze-drying method of the present invention may be any solvent that dissolves and swells the porous layer material and the non-porous layer material.
  • the porous layer material and the non-porous layer material are both poly- tan, 1,4-dioxane, tetrahydrofuran, N , N — Dimethylformamide and N, N — Dimethylacetamide can be used.
  • the freezing temperature can be appropriately changed according to the membrane material and the solvent, but the freezing temperature must be lower than the freezing point of the membrane material solution (B).
  • Non-porous layer of the present invention A membrane having a three-layer structure of a porous layer / a non-porous layer can be produced by using a pore-forming agent-added extraction method.
  • a nonporous membrane is first prepared by a cast method or the like. Thereafter, a two-layer film is formed on the film by using the pore-forming-agent-addition extraction method, thereby obtaining a three-layer film as shown in FIG. And can be done.
  • the three-layer membrane of the porous layer Z, the non-porous layer Z, and the porous layer can be obtained by a combination of a pore-forming-agent-added extraction method and a freeze-drying method.
  • a two-layer film of a non-porous layer and a porous layer is prepared by using the pore-forming agent addition extraction method, and the freeze-drying method is performed on the non-porous layer. This is what you get.
  • the artificial cornea of the present invention is made of an optically transparent material, and has an optical part having a front surface, a rear surface, and a side surface, and an external part from the side surface of the optical part. It has a human corneal body consisting of a protruding hub and a support part surrounding at least a part of the side surface of the optical part. The one using the medical membrane as a support part. Furthermore, the human cornea of the present invention replaces the entire layer, superficial layer or deep layer of the cornea in consideration of the state of the cornea having a reduced or lost function, and It restores visual function.
  • the optical section used for the artificial cornea of the present invention is made of an optically transparent material. Such an optical part is located almost at the center of the artificial cornea, and fulfills its visual function by maintaining transparency (transparency).
  • the material used for the optical part is harmless to the human body because the inner surface (rear surface) of the artificial cornea may come into direct contact with the aqueous humor in the eye. It is preferred that it be excellent in safety, such as contact with living organisms such as contact lenses, intraocular lenses, etc., or transplantation into living organisms. Material It is possible to use the used materials.
  • Examples of the above materials include acrylic resins and polybutyl acrylates represented by, for example, polymethyl methacrylate. Polyester, Polyurethane, Silicon, etc., represented by acrylic elastomers, polyethylene terephthalates, etc.
  • Non-hydrous materials such as polystyrene; poly 2 — hydroxy shechil methacrylate, poly vinyl alcohol, poly N — hydro hydrate such as biel pyrrolidone The raw materials are extinguished, and one or more of these materials are selected and used.
  • the planar shape of the optical section is not particularly limited, and may be any shape as long as there is no problem in practical use. In order to prevent deformation due to the pressure of the corneal surface, and in the case of ordinary corneal transplantation, it is often the case that a corneal replacement part is removed with a circular treadpan. Considering the points and the like, the shape is preferably a circle.
  • the planar shape of the optical section is circular, its diameter is determined unequivocally because the diameter differs depending on the size of the portion of the eye tissue to be replaced with the artificial cornea. I can't do that.
  • the reason is that the diameter between the ends of the support portion (outer diameter of the support portion) differs depending on the size of the tissue to be replaced, and therefore, the component part of the optical portion is required.
  • the diameter of the part is determined in consideration of the width of the supporting part where the visual function is not impaired and the suturing property and the penetration of eye tissue can be exhibited. In consideration of these facts, and from a practical point of view, it is preferable that the diameter of the optical section is usually about 2 to 8 mm, particularly about 3 to 7 mm. Yes.
  • the thickness of the optical section is preferably at least about 0.1 mm from the viewpoint of mechanical strength. Thickness
  • the thickness of the central part and the peripheral part may be changed, and for example, at least one of the optical parts is required.
  • the part should be a spherical surface. In particular, in order to provide a lens power to the optical unit, it is sufficient to provide spherical surfaces having different curvatures on the front surface and the rear surface of the optical unit.
  • the thickness of the optical part, the support part, and the collar at the boundary between the optical part and the support part the thickness of the optical part is smaller than the sum of the thickness of the support part and the thickness of the collar. There are no restrictions, no matter how large or large. However, since the irritation due to friction with the eyelid conjunctiva during blinking can be reduced, the thickness of the optical part is determined by the sum of the thickness of the support part and the collar part. It is also preferred that they are small or similar.
  • the artificial cornea of the present invention is provided with a torso portion projecting outward from the side of the optical portion, and the optical portion and the torso portion are combined to form an artificial cornea body.
  • optical part and the collar part of the artificial cornea of the present invention may be integrated or separate.
  • the tongue protrudes outward from the side of the optical part, but the tongue is located on the side of the optical part so that its rear surface and the rear surface of the optical part are flush with each other. And are preferred.
  • the collar serves as an adhesive substrate portion between the artificial corneal body and the support.
  • the supporting portion is used for suturing to eye tissue, the supporting portion is preferably bonded to the front surface of the collar portion.
  • the material used for the collar is harmless to the human body, As far as it is excellent in safety and achieves the purpose of the present invention, there is no particular limitation, for example, in the above-mentioned optical section. The same materials used can be used.
  • the lid portion protrudes outward from the side surface of the optical unit, and its planar shape is not particularly limited as long as the object of the present invention can be achieved. However, it is preferable that the annular shape is used in order to uniformly adhere to the supporting portion having an appropriate annular shape.
  • the inner diameter of the collar is the same as the diameter of the optical part, and the outer diameter of the collar serves as a joint board with the support.
  • the diameter of the optical part is preferably at least 0.5 mm or more.
  • the outer diameter of the collar portion may be larger or smaller than the outer diameter of the support portion. From these facts, it is preferable that the outer diameter of the tongue portion is about 2.5 to 20 mm.
  • the collar be provided with a curvature, and that the curvature be approximately equal to the curvature of the cornea. It is better.
  • the thickness of the collar (in the direction of the optical axis of the eye) is such that in the case of full-thickness transplantation, it is easy to insert the inside of the eye and the distance between the collar and the iris. It is 1 mm or less, preferably 0.05 to 0.5 mm, taking into account the separation of the anterior chamber and the volume of the anterior chamber, and so as not to adversely affect the eyes. This is desirable. In the case of superficial or deep layer transplantation, the thickness should be 1 mm or less, preferably 0.05 to 0.5 mm, considering the thickness of the cornea. No.
  • the thickness of the brim portion is at least 0.05 mm, for example. .
  • the artificial cornea of the present invention is provided with a protruding portion in which the collar portion protrudes outside of the supporting portion. That is, the outer diameter of the collar portion is made larger than the outer diameter of the support portion, and such a protruding portion can be provided.
  • the protruding portion of the collar is located in the eye chamber adjacent to the inner surface (posterior surface) of the cornea, and the artificial cornea floats outward from the cornea. Plays the role of a stopper for preventing climbing.
  • the protruding portion has a shape such that the corneal incision wound surface, which is a wound, is captured from the inside of the eye chamber, and the proliferation of cell tissue from the corneal incision wound surface.
  • the protrusion into the posterior surface of the artificial cornea is physically blocked and prevented at the protruding portion.
  • the prosthesis of the artificial cornea can be prevented from rising or falling off, and the cell tissue grown from the corneal incision wound surface can be optically clarified.
  • the optical part does not reach the rear surface, and the transparent part of the optical part (transparency) is reliably maintained. Also, in the case of superficial or deep layer transplantation, the protruding part is placed between the corneal layers to further prevent the artificial cornea from rising and falling off. You can do what you want.
  • the protruding portion protrudes outward from the support portion, and the shape thereof is such that the shape is excellent in safety and can achieve the object of the present invention.
  • the support portion is formed so as to protrude in an annular shape radially outward, so that the effect of the present invention can be effectively exhibited. Is preferred.
  • the collar portion protrudes more than 0.05 mm radially outward from the support portion in the radial direction, and furthermore, it is easy to insert into the eye. Considering,
  • a support is used for fixing the artificial cornea body including the optical part to eye tissue. That is, the artificial cornea is fixed by suturing the supporting portion and the eye tissue (cornea).
  • the support section is characterized by using a medical film having a porous layer and a non-porous layer, and surrounds at least a part of the side face of the optical section. It is set up to support it.
  • the outer side surface of the support is in contact with at least a part of the incision wound surface of the incised cornea.
  • the support used in the present invention has a porous layer
  • the surrounding eye tissue is inserted into the pores of the porous layer of the support.
  • Invasion results in the artificial cornea and the ocular tissue becoming tightly and affinity-bound, such as by anchoring.
  • the porous structure of the porous layer is not destroyed by using the surface of the non-porous layer for adhesion between the supporting portion and the brim portion of the artificial corneal body. Adhesion is possible, and a sufficient hole for penetration of ocular tissue can be secured.
  • a porous layer and a non-porous layer are alternately laminated, and at least one layer is laminated on each layer. It is preferable that the number of layers is 2 Or, a value of 3 is more preferred. It is even more preferred that the non-porous layer be present on at least one surface.
  • the supporting portion has flexibility. Since the supporting portion has flexibility, suturing of the eye tissue and the artificial cornea can be easily performed through the supporting portion, and it is easy to conform to the incision shape of the eye tissue. Furthermore, physical pressure on the eye tissue is reduced.
  • the shape stability of the support portion is greatly improved by including the non-porous layer.
  • the cut surface is crushed by the presence of the non-porous layer. It has the advantage that it can be molded without any problems.
  • the support portion has a mechanical strength not to be broken by suturing, and has a hole through which the surrounding ocular tissue can enter. It is preferred that it be of biocompatibility, such as contact with or in contact with living organisms such as contact lenses, intraocular lenses, etc. Materials that can be used for transplantation can be used.
  • Examples of the above-mentioned materials include, for example, an acrylic resin represented by a polymethyl methacrylate, a polyacryl acrylate, and the like. Polyester, polyurethane, silica, etc. represented by acrylic elastomers, polyethylene terrefu, and evening rates Non-hydrous materials such as polystyrene, polypropylene, and Teflon; Poly 2—Hydroxy Shechil Methacrylate, Polyvinyl Alcohol, Polystyrene Re-N—Hydrophilic materials such as vinyl pyrrolidone; bio-derived materials such as collagen; polylactic acid, polyglycolic acid and their Biodegradable polymers such as copolymers are used, and one or more of these are selected and used.
  • an acrylic resin represented by a polymethyl methacrylate, a polyacryl acrylate, and the like.
  • Polyester, polyurethane, silica, etc. represented by acrylic elastomers, polyethylene terrefu, and evening rates
  • the average pore size into which the cell tissue can enter is 1 to 500 ⁇ m, preferably 5 to 200 / im, more preferably 10 to 150 ⁇ m. m. Therefore, even the porous layer portion of the support portion used in the present invention has a porous layer having a pore diameter in a range of almost this range. You should.
  • the multiporous structure is preferably a bicontinuous structure so that ocular tissue can penetrate.
  • the state of the pores on the front surface thereof is not limited, and there are no pores and no pores. It may be in any state, such as dotted or porous. If the front surface is non-porous, it can prevent invasion and infection of bacteria, viruses, etc. Also, in the open state, the tissue that has developed on the front surface of the support portion and the tissue that has penetrated into the hole of the support portion interact through the hole and interact with each other. Can be done.
  • the planar shape of the support portion is not particularly limited, and may be any shape as long as there is no problem in practical use, but it is usually a circular treadpan. Concentric circles are often removed because they often remove the corneal replacement, maintain their mechanical strength, and prevent deformation due to intraocular pressure. Preferably, it is annular.
  • the inner diameter is usually about the same as the diameter of the optical portion.
  • the outer diameter cannot be determined unconditionally because it differs depending on the size of the portion of the eye tissue to be replaced with the artificial cornea, and the like, but it is not usually determined.
  • the incised eye tissue at the replacement site (cut The size should be the same as the size of the corneal segment (excluded), or about 0.5 mm, for example, about 4 to 20 mm, especially about 5 to 16 mm. This is preferable in practical terms.
  • the thickness of the support portion is not absolutely normal, but is usually about 0.01 to 3 mm, especially about 0 :! About 2.5 mm is preferable in practical terms.
  • the thickness of the support portion is almost the same as the thickness of the corneal incision section in the case of full-thickness transplantation in order to reduce irritation due to friction with the eyelid conjunctiva during blinking. It is preferred that it be or is somewhat thin.
  • the sum of the thickness of the support part and the brim part is almost the same as the thickness of the corneal incision section, or is slightly thinner. And are preferred.
  • the porous layer needs to be thick enough to allow the penetration of the ocular tissue, and the thickness is preferably at least 0.05 mm That is all.
  • the non-porous layer in the support portion of the present invention needs to have a thickness that can sufficiently serve as an adhesive surface, and the thickness is small. It is at least 0.001 mm.
  • the support portion has a curvature substantially equal to the curvature of the cornea.
  • the porous structure of the support is used. Since the nutrients from the aqueous humor may not be sufficiently supplied to the ocular tissue that has entered, it is necessary to supply nutrients from the rear side of the collar so that nutrients can be supplied. It may have a through-hole reaching the porous layer of the support.
  • the knuckle portion has a protruding portion that protrudes outside the support portion, nutrients are supplied to the corneal portion that comes into contact with the protruding portion.
  • the protruding portion may have a through hole.
  • the shape of the through-hole is not particularly limited as long as the purpose of the present invention can be achieved, and for example, a circular shape, a square shape, a rectangular shape, and the like are defined. .
  • the order to perform the functions will have a transmission of nutrients aqueous humor or al, the area of its is Ru Ah at 1 X 10- 6 mm 2 or more In order to maintain the strength of the collar portion, the thickness is preferably 100 mm 2 or less.
  • the atmosphere of the through hole is usually 1 X 10 6 ⁇ : LOOmm 2 about, and the Oh Ru this in 1 X 10- 2 ⁇ 30mm 2 about is good or was not in a practical point of view to the Ku.
  • the number of through-holes provided in the flange portion is not particularly limited as long as the object of the present invention can be achieved.
  • the number of through-holes may be one, and a plurality of through-holes may be provided. But it may be.
  • the state of distribution of the through-holes if there is a protruding portion of the eye tissue in the supporting portion, the corneal tissue on the brim portion of the protruding portion is present.
  • the density of the through-holes in the brim portion be uniform.
  • the center of the through hole is uniformly present on a concentric ring centered on the optical department.
  • the artificial cornea of the present invention comprises the optical part, collar, and support part as described above.
  • conjunctival valve covering, mucosal covering, amniotic covering, covering with an appropriate infection prevention sheet, etc. Is applied to part or all of the front of the transplant site. By covering the transplant site with these living tissues or sheets, intraocular infections and the like can be prevented.
  • a medical membrane having a three-layer structure of a non-porous layer Z, a porous layer, and a non-porous layer is used as a support for the artificial cornea, and the outer surface of the support is defined as a non-porous layer.
  • FIGS. 1, 2 and 3 are all scanning micrographs showing one embodiment of the medical film of the present invention.
  • the medical membrane 1 of the present invention has a structure in which a porous layer 2 and a non-porous layer 3 are laminated.
  • the medical membrane 1 of the present invention has a two-layer structure in FIGS. 1 and 2, and a three-layer structure of a non-porous layer 3 a / porous layer 2 / non-porous layer 3 b in FIG. , But is not limited to these, and may have two, three, or more layers.
  • the medical membrane 1 of the present invention thus obtained comprises a porous layer 2 having a uniform pore size and a non-porous layer 3, and the surface of the non-porous layer is used as a bonding surface.
  • the porous structure can be bonded to various medical substrates without destroying the porous structure.
  • the three-layer film as shown in FIG. 3 has non-porous layers 3a and 3b, one of which is used as a bonding surface, and the other is sterilized from the outside, and It can be used as a layer to prevent invasion and infection of viruses and the like.
  • FIG. 4 is a schematic cross-sectional view showing one embodiment of the artificial cornea of the present invention
  • FIGS. 5 (a) and 5 (b) are schematic plan views corresponding to the schematic cross-sectional view of FIG. It is.
  • One embodiment of the artificial cornea 4 is a case where a medical film having a two-layer structure of a non-porous layer 3 and a porous layer 2 is used as the support 6.
  • FIG. 5 (a) is viewed from the front side of the artificial cornea 4 (upper side of the schematic cross-sectional view)
  • FIG. 5 (b) is the posterior side of the artificial cornea 4. (Lower side of schematic sectional view).
  • FIG. 5 (a) is viewed from the front side of the artificial cornea 4 (upper side of the schematic cross-sectional view)
  • FIG. 5 (b) is the posterior side of the artificial cornea 4. (Lower side of schematic sectional view).
  • FIG. 5 (a) is viewed from the front side of the artificial cornea 4 (upper side of the schematic cross-section
  • FIG. 5 (a) the front surface of the support portion 6 schematically shows that holes are scattered, and the open state of the front surface and the distribution state of the holes are shown. There is no particular limitation, and the state may be non-porous, dotted with holes, or porous.
  • FIG. 5 (b) shows that the surface 3c of the non-porous layer 3 of the support portion 6 is adhered to the front surface 7a of the collar portion 7 (see FIG. 5B). See Figure 4).
  • the artificial cornea 4 in FIG. 4 includes an optical part 5 having a front surface 5a, a rear surface 5b, and a side surface 5c, a support part 6 surrounding the side surface 5c of the optical unit 5, and the like. And a flange portion 7 projecting outward from a side surface 5 of the optical portion 5 to cover a rear surface 6a of the support portion 6 and adhered to a front surface 7a thereof. Further, a protruding portion 8 of a tongue portion 7 protruding outward from the support portion 6 is provided. The projection 7 protrudes outward from the side surface 5c of the optical unit 5 so that the rear surface 7b and the rear surface 5b of the optical unit 5 are flush with each other. Further, the artificial cornea 4 of the present invention is characterized in that the medical membrane is used as the support portion 6.
  • the artificial cornea 4 shown in FIG. 4 has an integrated optical cornea composed of an optical part 5, a collar part 7, and a protruding part 8 of the collar part 7, and a support part. It is bonded to 6.
  • the hub part may be integrated with a part of the optical part or may be separate from the optical part.
  • the cornea is not limited to the number of components as described above.
  • the integrated part of the optical part, the nose part and the projection part of the head part can be obtained by, for example, compression molding, injection molding, cutting molding, or the like.
  • the 4 is a medical membrane of the present invention having a two-layer structure of a porous layer 2 and a non-porous layer 3, and is manufactured by the method described above. be able to .
  • the non-porous layer 3 is present on one surface of the support portion 6, and the surface 3c of the non-porous layer 3 is bonded to the front surface 7a of the collar portion 7 of the artificial corneal body. Used for surfaces.
  • the artificial cornea of the present invention has a great feature in its supporting portion.
  • the support is, for example, shown in FIGS.
  • Various membranes having a porous layer and a non-porous layer as shown in Fig. 3 can be used. Anything that can achieve the objectives of the invention is irrelevant.
  • the method of bonding the support portion and the artificial corneal body collar according to the present invention is to bond using a soluble solvent to both the material of the support and the artificial corneal body collar.
  • the method of bonding using an adhesive etc. is required.
  • the artificial cornea of the present invention thus obtained can be used to penetrate ocular tissues by using the non-porous layer of the support for the bonding surface when bonding the support to the main body. It is bonded without blocking or crushing the pores in the porous layer of the support part that serves as a scaffold for the porosity, and has a porous structure after transplantation of the human cornea.
  • the penetration of the eye tissue into the stratum corneum allows the artificial cornea and the eye tissue to be well fused.
  • the outer surface of the support also has a non-porous layer, it can prevent the invasion and infection of bacteria, viruses, etc. from the outside. It is a thing.
  • Fig. 6 shows a scanning microscope in which the medical membrane of the present invention is used as a support for an artificial cornea, and a portion of the artificial cornea that is adhered to the collar of the artificial cornea is observed from the lateral direction of the artificial cornea. It is a photograph.
  • the knuckle portion 7 and the support portion 6 of the artificial cornea are firmly adhered to the non-porous layer 3 of the support portion 6 and the front surface 7a of the brim portion 7. . Further, it is shown that the pores of the porous layer 2 are not closed or crushed by the bonding.
  • the artificial cornea 4 shown in FIGS. 7 (a) and 7 (b) has an optical part 5 having a front surface 5a, a rear surface 5b and a side surface 5c, and a side surface of the optical unit 5. 5c A part formed integrally with the flange 7 protruding outward from the force and the protrusion 8 of the flange 7 and the support 6 are separately manufactured.
  • the surface 3c of the non-porous layer 3 which is the rear surface 6a of the support portion 6 and the front surface 7a of the metal portion 7 were adhered using a solvent or the like as appropriate. That is, it can be obtained by providing a through-hole 9 extending from the rear surface 7b of the collar portion 7 to the porous layer 2 of the support portion 6.
  • the brim portion 7 protrudes beyond the support portion 6.
  • the projecting portion of the hub is not an essential component, but the hub preferably has a projecting portion.
  • the artificial cornea 4 shown in FIGS. 4, 6 and 7 (a) has a curvature, but the artificial cornea of the present invention has However, it is not limited to the presence or absence of curvature.
  • FIG. 8 is a schematic cross-sectional view of one embodiment showing an implanted state when the entire cornea is replaced with an artificial cornea (all-layer implant).
  • the outer side surface 6b of the support portion 6 and the incision wound surface 10a of the cornea 10 are in contact with each other.
  • the protruding portion 8 of the tongue portion 7 is located in the eye chamber so as to be adjacent to the inner surface (rear surface) 10b of the cornea 10. ing .
  • the artificial cornea is fixed by suturing the support portion 6 and the cornea 10 with the suture 11.
  • FIG. 9 (a) shows the cross section of the interface between the artificial cornea 4 and the rabbit cornea 10 for the cornea 10 of a Japanese white rabbit transplanted with the artificial cornea 4 during the transplantation period. This is a photograph observed by toluidine blue tissue staining two months later, and FIG. 9 (b) is a sketch for explaining FIG. 9 (a). .
  • FIG. 9 (a) only the cell tissue portion was stained.
  • the porous layer 2 the non-porous layer 3
  • the material portion of the artificial cornea 4 at the protruding portion 8 of the lid portion 7 and the collar portion 7 is not stained.
  • FIG. 9 (a) the stained tissue is shown in black because it is black and white, but in fact it is almost blue-violet.
  • FIG. 9 (b) is a sketch diagram of FIG. 9 (a), reference numerals 2, 3, 3c, 7, 7a and 7a in FIG. 9 (a)
  • Fig. 9 (a) is black and white.
  • FIG. 9 (a) it can be seen that the eye tissue of the rabbit cornea 10 has penetrated into the portion corresponding to the hole 2a of the porous layer 2 of the support portion 6 and has been fused at the interface. I do. Further, no ocular tissue of the rabbit cornea 10 is present at the position where the non-porous layer 3, the protrusion 7 and the protrusion 8 of the hook 7 are present.
  • the non-porous layer 3 and the tongue portion 7 are firmly adhered to the front surface 3c of the non-porous layer 3 and the front surface 7a of the tongue portion 7, and the collar is further
  • the protruding part 8 of the part 7 is the rotation of the eye tissue to the posterior surface of the artificial cornea It is also observed that the intrusion is blocked.
  • a medical membrane 1 comprising the porous layer 2 and the non-porous layer 3 shown in FIG. 1 was produced.
  • a medical membrane was produced by changing the pore diameter of the porous layer from the membrane described in Example 1.
  • Example 3 [Preparation of two-layer membrane by freeze-drying method] A medical membrane 1 composed of a porous layer 2 and a non-porous layer 3 shown in Fig. 2 was produced.
  • a commercially available polyurethan for medical use was dissolved in tetrahydrofuran to prepare a solution having a concentration of 4.0% by weight. 6.3 g of the solution was cast on a glass cylinder having a diameter of 4 cm, and the tetrahedral port was vaporized.
  • the cast membrane of polyurethan ( A non-porous layer 3) was prepared. 1.5 g of a 1,4-dioxane solution of 5.0% by weight of polyurethane was cast on the prepared membrane, and the surface of the non-porous layer 3 was dissolved in the solution.
  • the solution was frozen at 20 ° C in a swollen state.
  • the 1,4-dioxane was sublimated and removed under reduced pressure to obtain a polyurethane film.
  • the cross section of the prepared membrane was observed in the same manner as in Example 1 except that the magnification was set to 75 times.
  • the membrane 1 formed a two-layer structure of a porous layer 2 and a non-porous layer 3. It was confirmed that they were working.
  • the interface was integrated, and it was observed that the porous layer 2 had continuous pores having a diameter of about 10 to 50 ⁇ m.
  • the overall thickness of the membrane was 0.5 mm, and the thickness of the non-porous layer 3 was 0.1 mm.
  • polyurethan for medical use was dissolved in tetrahydrofuran to prepare a solution having a concentration of 5.0% by weight. Then, the solution l.O.Og is cast on a glass jar with a diameter of 4 cm, and the tetrahydrofuran is vaporized to obtain a polyurethan cas. A membrane (non-porous layer 3b) was produced. Polyurethane and sodium chloride were added to a 4.0% polyurethan solution in tetrahydrofuran. Sodium chloride was mixed and dispersed so that the weight ratio of sodium chloride to the total weight of the stream was 70% by weight.
  • sodium chloride those selected using a sieve having openings of 53 ⁇ m and 106 ⁇ m were used. 8.2 g of a suspension of the above tetrahydrofuran solution in which sodium chloride was sufficiently dispersed was cast on a cast membrane. Sodium chloride was precipitated in the solution, and then tetrahydrofuran was vaporized and removed. The resulting mixed membrane of polyurethane and sodium chloride was immersed in distilled water to extract sodium chloride. This was dried to obtain a polyurethane film.
  • the film had a three-layer structure in which the porous layer 2 was sandwiched between the non-porous layers 3 from both sides. The situation was confirmed. In addition, the interface was integrated, and it was observed that the porous layer 2 had continuous pores having a diameter of about 50 to 100 111. Further, the overall thickness of the membrane 1 was 0.8 mm, and the thickness of each of the non-porous layers 3a and 3b was 0.2 mm.
  • Example 5 Production of artificial cornea using membrane of Example 1
  • the optical part 5 and the tongue part 7 protruding from the side surface 5c of the optical part 5 to the outside of the ring.
  • the body of the artificial cornea shown in Figs. 4, 5 (a) and 5 (b) with the projection 8 of the corneal body (the optics is 0.9mm thick, 4.0mm outer diameter, front The radius of curvature was 8.0 mm, the rear surface had a radius of curvature of 7.1 mm, and the knob had a thickness of 0.2 mm, an outer diameter of 7.5 mm, a front surface radius of curvature of 7.3 mm, and a rear surface radius of curvature of lmm).
  • the polyurea silicone membrane described in Example 1 is punched into a donut shape using a 4 mm and 7 mm diameter trepan. Then, the non-porous layer 3 is fitted to the optical part 5 of the artificial corneal body such that the non-porous layer 3 is on the rear side of the support part 6, and the surface 3c of the non-porous layer 3 of the polyurethane film is The front surface 7a of the tongue portion 7 of the cornea body was bonded to the front surface 7a using tetrahydrofuran (see Fig. 4).
  • Figure 6 shows the result of observing the bonding portion between the collar 7 and the support 6 of the fabricated artificial corneal body. It was confirmed that the non-porous layer 3 of the support portion 6 and the front surface 7a of the collar portion 7 of the artificial corneal body were firmly adhered. In addition, it was confirmed that the porous layer 2 of the support portion 6 was present without being closed or crushed by the bonding.
  • Example 6 Production of artificial cornea using membrane obtained from Example 2
  • the main body of the artificial cornea was prepared in the same manner as in Example 5.
  • the optical section has a thickness of 0.5 mm, an outer diameter of 4.0 mm, a front curvature radius of 8. Omm, and a rear curvature radius of 7.5 mm.
  • the collar section has a thickness of 0.1 mm and an outer diameter of 7 mm. .5mm, front radius of curvature 7.6mm, rear radius of curvature 7.5mm.
  • the polyurea membrane described in Example 2 As the supporting portion of the artificial cornea, the polyurea membrane described in Example 2 was used. This film is punched out in a donut shape using a 4 mm and 8 mm diameter trepan, and the optical part of the artificial corneal body is placed so that the non-porous layer is on the back side. Then, the surface of the non-porous layer of the polyurethan film and the front surface of the collar portion of the artificial corneal body were bonded using tetrahydrofuran. The support and the main body of the obtained artificial cornea were firmly adhered to each other, and it was confirmed that the pores of the porous layer of the support were not crushed.
  • the artificial cornea 4 prepared in Example 5 was applied to an excimer laser (laser gas: KrF, oscillation wavelength: 248 nm, device: INDEX 846 manufactured by Sumitomo Heavy Industries, Ltd.).
  • the perforated portion 7 of the artificial cornea 4 and the non-porous layer 3 of the support portion 6 are perforated by using a square having a square shape of 0.5 mm ⁇ 0.5 mm shown in FIG.
  • Six through-holes 9 were formed at equal intervals on a concentric ring centered on the optical part 5.
  • Example 8 Transplantation of artificial cornea
  • the main body of the artificial cornea was prepared in the same manner as in Example 5. (2) Preparation of support
  • the film formed a two-layer structure of a porous layer and a non-porous layer.
  • the interface was integrated, and it was observed that the porous layer had continuous pores having a diameter of about 30 to 50 ⁇ m.
  • the overall thickness of the membrane was 0.7 mm, and the thickness of the non-porous layer was 0.05 mm.
  • Bonding was performed in the same manner as in Example 5 except that the membrane prepared in the above (2) was used as a support for the artificial cornea.
  • the support and the main body of the obtained artificial cornea were firmly adhered to each other, and it was confirmed that the pores of the porous layer of the support were not crushed.
  • the artificial cornea prepared as described above was sterilized with ethylenoxide and then transplanted into the cornea of a Japanese white rabbit.
  • all layers of the cornea of a Japanese white rabbit were punched out with a 6.5 mm diameter trepan, and the punched-out portion of the cornea had a protruding portion of the inner surface of the cornea.
  • the artificial cornea is inserted so as to be located in the eye chamber so as to be adjacent to the (rear surface), and the peripheral cornea and the supporting portion of the artificial cornea are joined using a nylon suture. I did it by doing
  • FIGS. 9 (a) and 9 (b) Histological observation of the artificial corneal transplant eye (trisymbol monochromatic color) revealed that the artificial cornea support 6 had a porous structure as shown in FIGS. 9 (a) and 9 (b). It was observed that the ocular tissue (corneal tissue) penetrated into the hole 2a of the layer 2, and the artificial cornea 4 and the cornea 10 of the Japanese white rabbit were firmly fused. By doing so, the pore structure of the porous layer 2 of the support portion 6 is not destroyed during the production of the artificial cornea (adhesion of the collar portion 7 of the main body and the support portion 6), and the eye is not damaged.
  • the medical film having the non-porous layer of the present invention on its surface is used in combination with another medical substrate, for example, the adhesion between the medical substrate and the film
  • the surface of the non-porous layer is used as the bonding surface, so that the bonding can be performed without affecting the porous structure of the porous layer. It is possible to join.
  • the non-porous layer is used for the interface with the outside world, invasion of bacteria, viruses, etc. from the outside. It can prevent infestation and prevent infection.
  • the presence of the non-porous layer provides excellent shape stability of the film itself, and also facilitates molding.
  • a porous layer and a non-porous layer alternately laminated in two or three layers are preferably used.
  • the nonporous layer surface of the supporting portion is used for the bonding surface with the artificial corneal body, so that the porous structure of the porous layer is not destroyed by the bonding.
  • the upper and lower surfaces are both non-porous layers, and if there is a porous layer between them, one surface of the non-porous layer is the main body. The other surface is at the interface with the outside world, and has an effect as an infection-preventing layer.
  • the pores of the porous layer are unnecessarily closed by a conventionally difficult joining method.
  • the non-porous layer of the supporting portion is used for the bonding surface with the artificial corneal body, and the supporting portion is bonded.
  • an artificial cornea can be produced without destroying the structure of the porous layer.
  • an area of the porous layer having a hole for penetration of eye tissue is secured, and after implantation of the artificial cornea into the eye, good penetration of eye tissue occurs.
  • the artificial cornea and the host cornea are firmly connected.

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  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Medicinal Chemistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Epidemiology (AREA)
  • Veterinary Medicine (AREA)
  • Dermatology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Dispersion Chemistry (AREA)
  • Engineering & Computer Science (AREA)
  • Composite Materials (AREA)
  • Materials Engineering (AREA)
  • Materials For Medical Uses (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne un film à usage médical dans lequel sont soudées au moins deux couches poreuse et non poreuse. L'invention concerne également une cornée artificielle pour laquelle le film susmentionné est utilisé en tant qu'élément de support pour fournir un élément de support capable de maintenir la structure poreuse sans dommage ou un élément de support empêchant l'invasion de bactéries et virus entre autres, de l'extérieur, ou l'infection provoquée par ces derniers.
PCT/JP2001/000917 2000-11-17 2001-02-09 Film a usage medical et procede de production de celui-ci, cornee artificielle faisant appel a ce film et procede de production de celle-ci WO2002039930A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
JP2002542307A JPWO2002039930A1 (ja) 2000-11-17 2001-02-09 医療用膜およびその製法、ならびにそれを用いた人工角膜およびその製法
AU2001232260A AU2001232260A1 (en) 2000-11-17 2001-02-09 Film for medical use and process for the production thereof, and artificial cornea with the use of the same and process for the production thereof

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JP2000351815 2000-11-17
JP2000/351815 2000-11-17

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2008093451A (ja) * 2002-08-09 2008-04-24 Ottawa Health Research Inst 眼用インプラント
JP2011139898A (ja) * 2009-12-08 2011-07-21 Jms Co Ltd 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
KR101796801B1 (ko) * 2009-08-13 2017-11-10 아큐포커스, 인크. 마스크형 안구 내 임플란트 및 렌즈
US11338067B2 (en) * 2017-03-30 2022-05-24 Marquette University Synthetic prosthesis for use in osteo-odonto-keratoprosthesis (OOKP) surgery

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH04158859A (ja) * 1990-10-23 1992-06-01 Seiko Epson Corp 人工角膜
WO1995020367A1 (fr) * 1987-07-07 1995-08-03 Jacob Labarre Jean T Protheses intra-oculaires
JPH09182762A (ja) * 1995-12-28 1997-07-15 Menicon Co Ltd 人工角膜
WO1998020813A1 (fr) * 1996-11-13 1998-05-22 Menicon Co., Ltd. Cornee artificielle

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1995020367A1 (fr) * 1987-07-07 1995-08-03 Jacob Labarre Jean T Protheses intra-oculaires
JPH04158859A (ja) * 1990-10-23 1992-06-01 Seiko Epson Corp 人工角膜
JPH09182762A (ja) * 1995-12-28 1997-07-15 Menicon Co Ltd 人工角膜
WO1998020813A1 (fr) * 1996-11-13 1998-05-22 Menicon Co., Ltd. Cornee artificielle

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2008093451A (ja) * 2002-08-09 2008-04-24 Ottawa Health Research Inst 眼用インプラント
KR101796801B1 (ko) * 2009-08-13 2017-11-10 아큐포커스, 인크. 마스크형 안구 내 임플란트 및 렌즈
JP2011139898A (ja) * 2009-12-08 2011-07-21 Jms Co Ltd 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
US11338067B2 (en) * 2017-03-30 2022-05-24 Marquette University Synthetic prosthesis for use in osteo-odonto-keratoprosthesis (OOKP) surgery

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AU2001232260A1 (en) 2002-05-27

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