WO2018211877A1 - 糸及びその製造方法 - Google Patents
糸及びその製造方法 Download PDFInfo
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- WO2018211877A1 WO2018211877A1 PCT/JP2018/015488 JP2018015488W WO2018211877A1 WO 2018211877 A1 WO2018211877 A1 WO 2018211877A1 JP 2018015488 W JP2018015488 W JP 2018015488W WO 2018211877 A1 WO2018211877 A1 WO 2018211877A1
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- A61F9/00—Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
- A61F9/007—Methods or devices for eye surgery
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K41/00—Medicinal preparations obtained by treating materials with wave energy or particle radiation ; Therapies using these preparations
-
- 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
- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
- A61L17/06—At least partially resorbable materials
- A61L17/08—At least partially resorbable materials of animal origin, e.g. catgut, collagen
-
- 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
- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
- A61L17/14—Post-treatment to improve physical properties
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/14—Macromolecular materials
- A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
- A61L27/24—Collagen
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
- A61L27/38—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/52—Hydrogels or hydrocolloids
-
- C—CHEMISTRY; METALLURGY
- C07—ORGANIC CHEMISTRY
- C07K—PEPTIDES
- C07K14/00—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof
- C07K14/435—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof from animals; from humans
- C07K14/78—Connective tissue peptides, e.g. collagen, elastin, laminin, fibronectin, vitronectin or cold insoluble globulin [CIG]
-
- D—TEXTILES; PAPER
- D01—NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
- D01F—CHEMICAL FEATURES IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS; APPARATUS SPECIALLY ADAPTED FOR THE MANUFACTURE OF CARBON FILAMENTS
- D01F4/00—Monocomponent artificial filaments or the like of proteins; Manufacture thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/16—Materials or treatment for tissue regeneration for reconstruction of eye parts, e.g. intraocular lens, cornea
Definitions
- the present invention relates to a yarn and a manufacturing method thereof.
- the present inventors have so far developed atelocollagen vitrigel membrane and demonstrated that damaged tissues such as skin, cornea, trachea, articular cartilage, tympanic membrane and esophagus can be regenerated.
- the atelocollagen vitrigel membrane is a biocompatible material having an epithelialization promoting effect and a scar formation inhibiting effect in the wound part.
- atelocollagen vitrigel membranes useful for skin tissue regeneration have already been researched and developed as medical devices by pharmaceutical companies and the like.
- artificial dermis made from atelocollagen that can be used in Japan includes Integra (registered trademark) (manufactured by Integra Life Science), Teldermis (registered trademark) (manufactured by Terumo) and Pernac (registered trademark) (manufactured by Gunze).
- Integra registered trademark
- Teldermis registered trademark
- Pernac registered trademark
- the present inventors have developed a technique for processing a native collagen vitrigel into an arbitrary shape such as a membrane, a thread, or a tube (for example, see Patent Document 1).
- telocollagen gel has less strength than native collagen gel
- the present invention has been made in view of the above circumstances, and provides a method for producing a yarn that can use a hydrogel having a lower strength than a native collagen gel as a raw material. Further, the present invention provides a yarn obtained by the above production method and having excellent strength.
- a columnar hydrogel can be irradiated with ultraviolet rays, vitrified, and rehydrated to produce a filamentous atelocollagen vitrigel.
- the present invention has been completed.
- the present invention includes the following aspects.
- the method for producing a yarn according to the first aspect of the present invention includes: A step A of irradiating the columnar hydrogel with ultraviolet rays; Step B obtained by vitrifying the columnar hydrogel after the ultraviolet irradiation to obtain a dried filamentous hydrogel, Rehydrating the dried filamentous hydrogel to obtain a filamentous vitrigel; and In this order.
- the yarn-shaped vitrigel may be re-glassed to obtain a dried filamentous vitrigel.
- a step E of reirradiating the dried filamentous vitrigel with ultraviolet rays may be provided.
- the yarn manufacturing method according to the first aspect may further include, after the step E, a step F of attaching or impregnating a hydrophobic solvent to the dried filamentous vitrigel re-irradiated with ultraviolet rays.
- the hydrogel may be atelocollagen gel.
- the yarn may be a tissue regeneration yarn that can be used as a suture.
- the yarn may be a cell transplant carrier.
- the yarn may be a conjunctival fistula filling material.
- the yarn may be a peritonitis inhibitor or a peritoneal fibrosis inhibitor.
- the yarn according to the second aspect of the present invention is made of a dried vitrigel, and is attached or impregnated with a hydrophobic solvent.
- the breaking strength of the yarn may be 0.1 kgf or more.
- the breaking strength of the yarn may be 0.2 kgf or more.
- the dried vitrigel may be a dried atelocollagen vitrigel.
- the hydrophobic solvent may be silicone oil.
- the thread may be a tissue regeneration thread that can be used as a suture.
- the yarn may be a cell transplant carrier.
- the yarn may be a filling material for the conjunctival fistula.
- the thread may be a peritonitis inhibitor or a peritoneal fibrosis inhibitor.
- yarn which can use the hydrogel which is not stronger than native collagen gel as a raw material can be provided. Moreover, the thread
- FIG. 2 is a graph showing the breaking strength of the dried filamentous atelocollagen gel 1 of each condition in Example 1.
- FIG. 2 is a graph showing the breaking strength of the dried filamentous atelocollagen vitrigel 2 under various conditions in Example 1.
- FIG. 2 is a graph showing the breaking strength of Polyglactin suture bicyclyl (registered trademark) under various conditions in Example 1.
- FIG. It is the image which sutured the mouse incision part using the filamentous atelocollagen vitrigel dry body 1 infiltrated with the silicone oil in Example 2.
- FIG. 6 is an image showing the results of staining a hematoxylin-eosin (HE) tissue section of a mouse suture part using dried filamentous atelocollagen 1 (infiltrate 1) infiltrated with silicone oil on day 7 of suture in Example 2; is there. It is an image which shows the result of carrying out HE dyeing
- HE hematoxylin-eosin
- Example 2 a tissue section of a mouse suture part using dried atelocollagen vitrigel 1 (infiltrate 1) infiltrated with silicone oil on the 7th day of suture was subjected to anti- ⁇ smooth muscle actin ( ⁇ -smooth muscle actin: ⁇ ).
- -SMA An image showing the result of immunostaining with an antibody. It is an image which shows the result of carrying out the immuno-staining by the anti- (alpha) SMA antibody the tissue section
- FIG. It is an image of the rehydrated filamentous atelocollagen vitrigel 1 (rehydrated 1) cultured with endothelial cells in Example 4. It is an image of the rehydrated filamentous atelocollagen vitrigel 1 (rehydrated 1) cultured with fibroblasts in Example 4.
- Example 4 is an image of a rehydrated polyglactin suture bicyclyl (registered trademark) (rehydrated body 3) cultured with fibroblasts in Example 4.
- 6 is an image of dried filamentous atelocollagen vitrigel (CXM1 and CXM5) used in Example 5. It is a figure which shows the insertion method in the mouse
- FIG. It is an image which shows a mode that the filamentous atelocollagen vitrigel dry body in Example 5 is inserted in the mouse
- the upper figure is an image showing the entire abdomen of the opened mouse, and the lower figure is an enlarged image of the peritoneum.
- the scale bar indicates 1 cm. 6 is an HE-stained image of a tissue section of each group of mice 40 days after the induction of peritonitis in Example 5.
- FIG. The upper figure is a HE-stained image of the wall-side peritoneum, and the lower figure is a HE-stained image of the visceral peritoneum.
- the scale bar indicates 100 ⁇ m.
- FIG. 6 is an Azan-stained image of a tissue section of the wall-side peritoneum of each group of mice 40 days after induction of peritonitis in Example 5.
- FIG. The scale bar indicates 200 ⁇ m.
- FIG. 6 is a graph showing the thickness of the subcutaneous connective tissue of the fibrotic peritoneum of each group of mice 40 days after induction of peritonitis in Example 5. It is an image which shows the mode of the peritoneum of each group of mice opened on day 56 after peritonitis induction in Example 5. The upper figure is an image showing the entire abdomen of the opened mouse, and the lower figure is an enlarged image of the peritoneum. The scale bar indicates 1 cm.
- FIG. 6 is a HE-stained image of a tissue section of each group of mice 56 days after induction of peritonitis in Example 5.
- FIG. 6 is a HE-stained image of a tissue section of each group of mice 56 days after induction of peritonitis in Example 5.
- the upper figure is a HE-stained image of the wall-side peritoneum
- the lower figure is a HE-stained image of the visceral peritoneum.
- the scale bar indicates 100 ⁇ m. 6 is an Azan-stained image of a tissue section of the wall-side peritoneum of each group of mice 56 days after induction of peritonitis in Example 5.
- FIG. The scale bar indicates 200 ⁇ m.
- FIG. 6 is a graph showing the thickness of the subcutaneous connective tissue of fibrotic peritoneum in each group of mice on day 56 after induction of peritonitis in Example 5.
- FIG. 9 is an immunostained image of various antibodies on tissue sections of the peritoneum of each group of mice 40 days after induction of peritonitis in Example 5.
- FIG. The scale bar of the immunostained image with anti-cytokeratin AE1 / AE3 (CK AE1 / AE3) antibody, anti-vimentin antibody and anti-N-cadherin antibody indicates 50 ⁇ m.
- the scale bar of the immunostained image with an anti-connective tissue growth factor (CTGF) antibody and anti- ⁇ -SMA antibody indicates 100 ⁇ m.
- FIG. 9 is an immunostained image of various antibodies on tissue sections of the peritoneum of each group of mice 40 days after induction of peritonitis in Example 5.
- FIG. The scale bar indicates 50 ⁇ m.
- SMIL mesothelial stroma layer
- PCNA proliferating cell nuclear antigen
- the yarn manufacturing method according to the first embodiment of the present invention includes: A step A of irradiating the columnar hydrogel with ultraviolet rays; Step B obtained by vitrifying the columnar hydrogel after the ultraviolet irradiation to obtain a dried filamentous hydrogel, Rehydrating the dried filamentous hydrogel to obtain a filamentous vitrigel; and In this order.
- a yarn can be manufactured using a hydrogel having a strength lower than that of the native collagen gel as a raw material.
- the details of each step of the yarn manufacturing method of the present embodiment will be described.
- the columnar hydrogel is irradiated with ultraviolet rays to increase the strength of the columnar hydrogel.
- the columnar hydrogel used in the step A may be any one obtained by, for example, using a cylindrical mold or the like so that the sol has a desired diameter.
- the temperature which heat-retains sol at the time of gelatinizing according to the kind of sol to be used is just to adjust suitably the temperature which heat-retains sol at the time of gelatinizing according to the kind of sol to be used.
- the heat retention during gelation may be lower than the collagen denaturation temperature depending on the animal species of the collagen used, and is generally 20 ° C. or higher and 37 ° C. or lower.
- the gelation can be performed in a few minutes to a few hours by keeping the temperature at.
- sol means that dispersoid colloidal particles (size: about 1 to several hundred nm) using a liquid as a dispersion medium are particularly composed of a polymer compound. More specifically, the sol is an aqueous solution of a natural product polymer compound or a synthetic polymer compound. Therefore, when a crosslink is introduced by a chemical bond of these polymer compounds to form a network structure, the polymer compound is transferred to a “hydrogel” that is a semi-solid substance having a large amount of water in the network. That is, “hydrogel” means a gelled sol. “Vitrigel” refers to a gel in a stable state obtained by rehydrating a conventional hydrogel after vitrification.
- Vitrigel (registered) Trademark) ”. Further, in the present specification, in describing the production process of the present embodiment in detail, the hydrogel dried body that has just undergone the vitrification process and has not undergone the rehydration process is simply referred to as “hydro. Gel dried body ". And the gel obtained through the rehydration process after the said vitrification process was distinguished and represented as "Vitrigel", and the dried body obtained by vitrifying the Vitrigel was referred to as "Vitrigel dried body”. Moreover, what was obtained by performing the step of irradiating the dried vitrigel with ultraviolet rays was referred to as “dried vitrigel dried with ultraviolet rays”. Therefore, “vitrigel” is a hydrate.
- the sol used as a raw material for the columnar hydrogel may be any material having biocompatibility, for example, an extracellular matrix-derived component that gels, natural polymer compounds such as fibrin, agar, agarose, and cellulose, and Synthetic polymer compounds such as polyacrylamide, polyvinyl alcohol, polyethylene oxide, poly (II-hydroxyethyl methacrylate) / polycaprolactone, and the like can be mentioned.
- extracellular matrix-derived component examples include collagen (type I, type II, type III, type V, type XI, etc.), mouse EHS tumor extract (type IV collagen, laminin, heparan sulfate proteoglycan, etc.) (Including, but not limited to) base membrane components (trade name: Matrigel), glycosaminoglycan, hyaluronic acid, proteoglycan, gelatin and the like. It is possible to produce a desired vitrigel by selecting components such as salt, concentration, pH and the like that are optimal for each gelation. Moreover, the vitrigel which imitated various in-vivo tissues can be obtained by combining raw materials.
- collagen type I, type II, type III, type V, type XI, etc.
- mouse EHS tumor extract type IV collagen, laminin, heparan sulfate proteoglycan, etc.
- base membrane components trade name: Matrigel
- glycosaminoglycan hyaluronic acid
- an extracellular matrix-derived component that gels is preferable, and collagen is more preferable.
- a more preferable raw material in collagen native collagen or atelocollagen can be illustrated, and atelocollagen is more preferable.
- atelocollagen gel is particularly preferable because it is a biocompatible material having an epithelialization promoting effect and a scar formation suppressing effect in a wound part.
- the hydrogel obtained from the sol exemplified above becomes a gel having a strength equivalent to that of the native collagen gel or a gel having a strength lower than that of the native collagen gel depending on the composition and content thereof. Further, the gel may be stronger than the native collagen gel. Even if it is hydrogel of any intensity
- the “epithelialization promoting effect” means that the formation of regenerative epithelium is promoted by suppressing the formation of granulation tissue and further promoting the proliferation of epidermal cells in the healing process of the wound part. Means. By using a thread made of dried atelocollagen vitrigel as a suture, epithelialization is promoted, so that the wound can be healed in a shorter period of time than before. Moreover, the “scar formation inhibitory effect” means an effect of suppressing the formation of a so-called scar (a scar) remaining after the wound has healed. By using a thread made of dried atelocollagen vitrigel as a suture, the wound can be treated without leaving a scar.
- the irradiation energy of the ultraviolet rays to the columnar hydrogel in this step is sufficient if the vitrification is performed in the state where the hydrogel is continued, for example, when vitrification is performed in a state where the columnar hydrogel is suspended. What is necessary is just to adjust suitably according to a composition and content of a gel.
- Columnar irradiation energy of the ultraviolet into the hydrogel may be, for example, if 0.1 mJ / cm 2 or more 6000 mJ / cm 2 or less, as long e.g. 10 mJ / cm 2 or more 4000 mJ / cm 2 or less, for example 100 mJ / cm 2 It is sufficient if it is 3000 mJ / cm 2 or more.
- the irradiation of the columnar hydrogel with ultraviolet rays is performed so that the ultraviolet irradiation region is divided into one surface and the other surface of the columnar hydrogel (for example, “upper surface”) so that the entire surface of the columnar hydrogel is irradiated with ultraviolet rays.
- the total irradiation amount may be set as the total irradiation amount of ultraviolet rays per unit area to the columnar hydrogel.
- Step B the dried columnar hydrogel is dried and vitrified to obtain a dried filamentous hydrogel.
- free water in the columnar hydrogel can be completely removed, and further partial removal of the bound water can proceed.
- the longer the period of this vitrification process the process of proceeding with the partial removal of bound water after completely removing the free water in the columnar hydrogel, the more excellent the transparency and strength when rehydrated. Vitrigel can be obtained. If necessary, the filamentous vitrigel obtained by rehydration after vitrification for a short period of time can be washed with PBS or the like to be vitrified again.
- a drying method for example, various methods such as air drying, drying in a sealed container (circulating air in the container and always supplying dry air), drying in an environment where silica gel is placed, and the like can be used.
- the air drying method include a method of drying in an incubator kept sterile at 10 ° C. and 40% humidity for 2 days, or drying at room temperature all day and night in a clean clean bench. it can.
- the columnar hydrogel since the columnar hydrogel has an appropriate strength by being irradiated with the ultraviolet rays in the above-mentioned step A, it can be efficiently dried in a state of being hung on a clothesline or the like during drying. it can.
- Step C Subsequently, the obtained dried filamentous hydrogel is rehydrated to obtain a filamentous vitrigel.
- rehydration may be performed using physiological saline, PBS (Phosphate Buffered Saline), or the like.
- yarn which concerns on 2nd Embodiment of this invention is a method provided with the process D which re-glass-forms the said filamentous vitrigel further after the said process C, and obtains a filamentous vitrigel dried body.
- a yarn can be produced using a hydrogel having a lower strength than a native collagen gel as a raw material. Steps A to C are as described in the first embodiment. Details of step D in the present embodiment will be described below.
- the obtained filamentous vitrigel is dried and vitrified again.
- the drying method include the same methods as those exemplified in Step B above. Further, in this step, since the filamentous vitrigel has an appropriate strength, it can be efficiently dried while being hung on a clothesline or the like.
- yarn which concerns on 3rd Embodiment of this invention is a method provided with the process E which reirradiates an ultraviolet-ray to the said filamentous vitrigel dried body after the said process D further.
- a yarn can be produced using a hydrogel having a lower strength than a native collagen gel as a raw material. Moreover, the yarn obtained by the production method of the present embodiment has excellent strength. Steps A to D are as described in the first and second embodiments described above. Details of step E in the present embodiment will be described below.
- the dried filamentous vitrigel product is further irradiated with ultraviolet rays to further increase the strength of the dried filamentous vitrigel product.
- the irradiation energy of the ultraviolet ray to the dried filamentous vitrigel in this step is not limited as long as the dried filamentous vitrigel is used as a suture or the like, depending on the composition and content of the dried filamentous vitrigel. What is necessary is just to adjust suitably.
- Filamentous UV irradiation energy to Bitorigeru dried body may, for example, if 0.1 mJ / cm 2 or more 6000 mJ / cm 2 or less, as long e.g. 10 mJ / cm 2 or more 4000 mJ / cm 2 or less, for example 100 mJ / cm as long as two or more 3000mJ / cm 2 or less.
- the total irradiation amount may be set as the total irradiation amount of ultraviolet rays per unit area to the dried filamentous vitrigel body, for example, “upper surface and lower surface” or “front surface and back surface”.
- the yarn manufacturing method according to the fourth embodiment of the present invention is a method including, after the step E, the step F of attaching or impregnating a hydrophobic solvent to the dried filamentous vitrigel that has been re-irradiated with ultraviolet rays. .
- a yarn can be produced using a hydrogel having a lower strength than the native collagen gel as a raw material. Further, the yarn obtained by the production method of the present embodiment has increased flexibility due to the hydrophobic solvent acting as a lubricant, and includes the hydrophobic solvent, so that even in the presence of an aqueous solvent. Strength can be maintained. Steps A to E are as described in the first embodiment, the second embodiment, and the third embodiment described above. Details of step F in the present embodiment will be described below.
- Step F the dried filamentous vitrigel after ultraviolet irradiation is attached or impregnated with a hydrophobic solvent.
- the flexibility of the dried filamentous vitrigel is increased, and when used in applications such as sutures, the hydrophobic solvent acts as a lubricant and can be smoothly sutured without catching the laceration.
- the hydrophobic solvent acts as a lubricant and can be smoothly sutured without catching the laceration.
- a hydrophobic solvent on the surface of the dried filamentous vitrigel or impregnating from directly under the surface to the inside, a decrease in strength due to rehydration by body fluid or the like is prevented at the sutured portion, and the yarn Strength is maintained.
- attachment means that a hydrophobic solvent is attached to the surface of the dried filamentous vitrigel
- impregnate means that the hydrophobic solvent is directly from the surface of the dried filamentous vitrigel to the inside. It means to be soaked.
- hydrophobic solvent used in this step is not particularly limited as long as it has biocompatibility, and examples thereof include hydrophobic solvents used in known medical applications.
- hydrophobic solvents include, for example, medical paraffin; liquid oils from plant, seafood, or animal sources (eg, olive oil, corn oil, soybean oil, canola oil, cottonseed oil, coconut oil, sesame oil, sunflower oil Borage seed oil, clove oil, hemp seed oil, herring oil, cod liver oil, salmon oil, flaxseed oil, malt oil, evening primrose oil, and mixtures thereof in any proportion); linole and linolenic acid, ⁇ -linoleic acid ( Polyunsaturated oils containing omega-3 and omega-6 fatty acids such as GLA), eicosapentaenoic acid (EPA), and docosahexaenoic acid (DHA); roses, chanoki, burdock, camphor, cardamom, carrots, kousaigaya Clary), s
- hydrophobic solvents may be used alone or in combination.
- the hydrophobic solvent is preferably silicone oil.
- Silicone oil may be unmodified or modified. More specific examples of the silicone oil include, but are not limited to, polydimethylsiloxane, polymethylphenylsiloxane, polydiphenylsiloxane, polymethylhydrogensiloxane, and the like.
- the temperature for attaching or impregnating the hydrophobic solvent is not particularly limited, and may be, for example, 10 ° C. or more and 40 ° C. or less.
- the time for attaching or impregnating the hydrophobic solvent is not particularly limited, and may be, for example, 30 minutes to 48 hours.
- Examples of the method for adhering or impregnating the hydrophobic solvent include a method of immersing the dried filamentous vitrigel in a hydrophobic solvent, a method of applying a hydrophobic solvent to the dried filamentous vitrigel, and spraying the hydrophobic solvent on the dried filamentous vitrigel. However, it is not limited to these.
- the yarn obtained by the production method of the present embodiment can be used as, for example, a tissue regeneration yarn, a cell transplant carrier, and the like, as shown in Examples described later.
- the yarn obtained by the production method of the present embodiment is used as a conjunctival fistula filling material to be used for inserting a treatment device into the vitreous body during a vitreous surgery, as shown in the following examples. Can do.
- yarn obtained by the manufacturing method of this embodiment can be used as an indwelling material which inserts in the abdominal cavity and suppresses peritonitis and peritoneal fibrosis as shown in the below-mentioned Example.
- yarn which concerns on one Embodiment of this invention consists of a vitrigel dry body, and the hydrophobic solvent adheres or is impregnated.
- the yarn of this embodiment is composed of a dried vitrigel, it has excellent strength and can be used as a suture or the like.
- the yarn of the present embodiment has increased flexibility due to the hydrophobic solvent acting as a lubricant, and can maintain strength even in the presence of the aqueous solvent by including the hydrophobic solvent. it can. Therefore, in the case where the thread of this embodiment is used as a suture, the suture part is maintained without being released after the operation.
- the shape of the cross section of the yarn of this embodiment is not particularly limited.
- a polygon such as a triangle, a quadrangle (including a square, a rectangle, a trapezoid), a pentagon, a hexagon, a heptagon, an octagon;
- Examples include, but are not limited to, a shape, a substantially circular shape, an elliptical shape, a substantially elliptical shape, a semicircular shape, and a sector shape.
- yarn is circular.
- the average diameter of the yarn may be, for example, from 1 ⁇ m to 1 mm, for example, from 3 ⁇ m to 900 ⁇ m.
- the breaking strength of the yarn of this embodiment may be a strength that does not cut when used in applications such as sutures.
- the breaking strength of the yarn may be, for example, 0.1 kgf or more, for example, 0.2 kgf or more.
- the yarn can have a strength that does not cut when used in applications such as sutures.
- the method for measuring the breaking strength of the yarn is as follows. Using a digital force gauge (manufactured by Nidec Simpo), cut the yarn to a total length of 5 cm, fix 1 cm at both ends, and measure the breaking strength (kgf) when pulled at 9 mm per minute . Next, the components of the yarn of this embodiment will be described in detail below.
- the yarn of this embodiment is made of a dried vitrigel.
- the sol that is a raw material for the dried vitrigel include the same materials as those exemplified in the above-described yarn production method.
- the dried vitrigel constituting the yarn of this embodiment is preferably a dried atelocollagen vitrigel because it is a biocompatible material having an epithelialization promoting effect and a scar formation suppressing effect in a wound part.
- the yarn of this embodiment is attached or impregnated with a hydrophobic solvent.
- the hydrophobic solvent include the same solvents as those exemplified in the above-described yarn production method.
- the hydrophobic solvent contained in the yarn of this embodiment is preferably silicone oil.
- the thread of the present embodiment is useful as a suture because it has excellent strength and the strength is maintained even in the presence of bodily fluids, etc., as shown in the examples described later. Furthermore, when the thread of this embodiment is used as a suture, tissue regeneration is promoted in the wound and no scar is formed. That is, the yarn of this embodiment is useful as a tissue regeneration yarn that can be used as a suture.
- the thread of the present embodiment is composed of a dried atelocollagen vitrigel, it has an effect of promoting epithelialization and suppressing scar formation in a wound part, and thus is suitable as a tissue regeneration thread.
- tissue regenerated yarn means a yarn that promotes tissue regeneration at the sutured portion.
- promotion of tissue regeneration specifically refers to promotion of wound contraction in the healing process of the wound, suppression of formation of granulation tissue, promotion of formation of regenerative epithelium by proliferation of epidermal cells, and the like.
- the yarn of this embodiment has excellent cell adhesion and cell proliferation as shown in the examples described later.
- desired cells can be cultured using the yarn of this embodiment, and the yarn with the cells adhered thereto can be transplanted into the living body of the subject. That is, the yarn of this embodiment is useful as a cell transplant carrier.
- the thread of this embodiment is useful as a material for conjunctival fistula preparation in order to insert a treatment device into the vitreous body during a vitreous surgery, as shown in the examples described later.
- the yarn of this embodiment when the yarn of this embodiment is composed of a dried atelocollagen vitrigel, it has an inhibitory action on inflammation and fibrosis of the wall-side peritoneum and visceral peritoneum, as shown in Examples below. Furthermore, it has an inhibitory action on the adhesion between the visceral peritoneum (intestinal tracts).
- the yarn of this embodiment is safe even when placed in a living body, and similarly has an inflammation-inhibiting action or a fibrosis-inhibiting action in tissues other than the peritoneum. That is, the yarn of this embodiment is useful as an inflammation inhibitor or a fibrosis inhibitor (particularly a peritonitis inhibitor or a peritoneal fibrosis inhibitor).
- yarn of this embodiment is useful as an intestinal adhesion inhibitor.
- filamentous atelocollagen vitrigel dried 1 a product manufactured using a 1 mL pipette (hereinafter sometimes referred to as “filamentous atelocollagen vitrigel dried 1”) is 148 ⁇ What was manufactured using a 5 mL pipette (hereinafter may be referred to as “filamentous atelocollagen vitrigel 2”) was 444 ⁇ 30 ⁇ m.
- Example 1 Test for confirming breaking strength of dried filamentous atelocollagen vitrigel The breaking strength of the dried filamentous atelocollagen 1 and the dried filamentous atelocollagen 2 produced in Production Example 1 was measured.
- a filamentous atelocollagen vitrigel dried body 1 hereinafter sometimes referred to as “dried body 1”
- rehydrated body 1 a filamentous atelocollagen vitrigel obtained by rehydrating the dried body 1
- infiltrate 1 dried filamentous atelocollagen vitrigel 1 infiltrated with silicone oil
- dried body 2 dried filamentous atelocollagen vitrigel 2
- rehydrated body 2 dried atelocollagen vitrigel rehydrated dry body 2
- rehydrated body 2 dried atelocollagen vitrigel 2 infiltrated with silicone oil
- polyglactin suture bicyclyl (7-0, average diameter of suture standard: about 50 to 69 ⁇ m) (hereinafter sometimes referred to as “dry body 3”), dry body 3 Rehydrated bicyclyl (registered trademark) (hereinafter sometimes referred to as “rehydrated body 3”) and bicyclyl (registered trademark) infiltrated with silicone oil (hereinafter sometimes referred to as “infiltrated body 3”). ) Also prepared.
- FIGS. 1A, 1B and 1C show the breaking strength.
- the dried body 1 and the infiltrating body 1 have almost the same breaking strength as that of the dry body 3, the rehydrated body 3 and the infiltrating body 3 of Bicuryl (registered trademark) as controls. It was. On the other hand, the rehydrated body 1 and the rehydrated body 2 had a breaking strength smaller than 0.1 kgf. Further, it was confirmed that the dried body 2 and the infiltrating body 2 had a breaking strength larger than 1 kgf and superior to the bicyclyl (registered trademark) dried body 3, the rehydrated body 3 and the infiltrating body 3 as controls. It was. This was presumed to originate from the size of the average diameter.
- Example 2 Suture test of mouse incision using dried filamentous atelocollagen vitrigel The dried filamentous atelocollagen 1 obtained in Production Example 1 was infiltrated with silicone oil (infiltrate 1) for surgery. In order to confirm that the strength was able to withstand, a suture test of the mouse epidermis incision was performed.
- FIG. 2 shows an image of the mouse on the day of suture.
- the infiltrating body 1 has sufficient strength as a suture and does not cause the wound to be separated after the operation.
- a tissue section of the sutured part on the 7th day of suture was prepared, and immunostaining was performed using hematoxylin-eosin (HE) staining and anti- ⁇ smooth muscle actin ( ⁇ -SMA) antibody.
- HE staining is shown in FIG. 3A
- ⁇ -SMA antibody is shown in FIG. 3C.
- a suture test of the mouse epidermis incision was performed using a polyglactin suture bicyclyl (registered trademark) (7-0, average diameter of suture standard: about 50 to 69 ⁇ m) (dry body 3) as a control.
- a tissue section of the sutured part on the seventh day of suture was prepared, and HE staining and immunostaining using an anti- ⁇ -SMA antibody were performed.
- the result of HE staining is shown in FIG. 3B, and the result of immunostaining with anti- ⁇ -SMA antibody is shown in FIG. 3D.
- Example 3 Filling test of porcine conjunctival fistula using dried filamentous atelocollagen vitrigel To confirm that dried filamentous atelocollagen gel 2 obtained in Production Example 1 (dried product 2) has excellent strength. In addition, it was used as a filling material in the conjunctival defect part (fistula part) of pigs.
- FIG. 4A shows an image of the conjunctival fistula of the pig on the day embedded as a filling material.
- the arrow indicates the embedded dry body 2.
- a plastic port that is usually used as a filling material for the conjunctival fistula was embedded. The result is shown in FIG. 4B.
- the arrows indicate embedded plastic ports.
- the dry body 2 has excellent strength and can be used as a filling material for closing the conjunctival fistula.
- Example 4 Cell Adhesion and Proliferation Confirmation Test Using Dry Filament Atelocollagen Vitrigel Dry Cellular Atelocollagen Vitrigel 1 in Production Example 1 (Rehydrated 1) is a good cell.
- a cell culture test using endothelial cells and fibroblasts was performed. Specifically, endothelial cells (MS-1, ATCC (American Type Culture Collection)) and fibroblasts (Wistar rat-derived primary cultured dermal fibroblasts) were each resected together with rehydrated body 1 cut to 5 cm. Cultured for 10 days.
- FIG. 5A is an image showing rehydrate 1 cultured with endothelial cells
- FIG. 5B is an image showing rehydrate 1 cultured with fibroblasts.
- the arrows indicate the endothelial cells adhered to the rehydrated body 1.
- FIG. 5C is an image showing rehydrated body 3 cultured with fibroblasts.
- Example 5 Peritoneitis suppression effect and peritoneal fibrosis suppression effect confirmation test using dried filamentous atelocollagen vitrigel Dry filamentous atelocollagen vitrigel 1 and dried filamentous atelocollagen vitrigel 2 produced in Production Example 1 were used as peritoneal fibers. We investigated the effect of indwelling in a model mouse.
- FIG. 6A is an image showing dried filamentous atelocollagen vitrigel 1 and dried filamentous atelocollagen vitrigel 2 produced in Production Example 1.
- FIG. 6A “CXM1” represents the dried filamentous atelocollagen vitrigel 1 and “CXM5” represents the dried filamentous atelocollagen vitrigel 2.
- FIG. 6B is a diagram showing a method for inserting a dried filamentous atelocollagen vitrigel into the abdominal cavity of a mouse.
- the dried filamentous atelocollagen vitrigel 1 and the dried filamentous atelocollagen vitrigel 2 were respectively inserted into the abdominal cavity of a female ICR mouse having a body weight of 40 g (see FIG. 6C).
- Sham group needle puncture only, chlorhexidine not intraperitoneal injection CG group: chlorhexidine intraperitoneal injection only Gel group: atelocollagen gel intraperitoneal injection, chlorhexidine intraperitoneal injection CXM group: filamentous atelocollagen vitrigel dry body intraperitoneal insertion, chlorhexidine intraperitoneal Injection
- FIG. 7A the results are shown in FIG. 7A (40 days after induction of peritonitis) and FIG. 8A (56 days after induction of peritonitis).
- FIG. 7A the arrowheads described in the CG group and the Gel group indicate adhesion between the peritoneum and the intestinal tract
- the arrow described in the Gel group indicates a collagen gel placed in the peritoneum
- the arrow described in the CXM group indicates the peritoneum.
- the indwelling filamentous atelocollagen vitrigel is shown.
- FIG. 8A the arrow head described in the CG group indicates adhesion between the peritoneum and the intestinal tract
- the arrow described in the CXM group indicates a filamentous atelocollagen vitrigel placed in the peritoneum.
- FIG. 7B HE-stained image
- FIG. 7C Azan-stained image
- FIG. 8B HE dyeing
- FIG. 8C Azan dyeing
- the upper figure is a HE-stained image of the wall-side peritoneum
- the lower figure is a HE-stained image of the visceral peritoneum.
- the scale bar indicates 100 ⁇ m.
- a scale bar shows 200 micrometers. Further, from the Azan stained images shown in FIG. 7C and FIG. 8C, the thickness ( ⁇ m) of the mid-subcutaneous connective tissue of each group of mice was measured, and the average value was graphed (see FIG. 7D and FIG. 8D).
- the fibrosis of the wall side peritoneum was significantly suppressed in the Gel group and the CMX group as compared with the CG group.
- the CMX group had a particularly remarkable effect of suppressing fibrosis of the wall side peritoneum than the Gel group.
- the fibrosis of the wall-side peritoneum was significantly suppressed in the CMX group as compared with the CG group at the 56th day after the induction of peritonitis. From this point on, the weight loss of the CG group was significant and the test could not be continued.
- Anti-cytokeratin AE1 / AE3 (CK AE1 / AE3) antibody CK AE1 / AE3 is a general-purpose epithelial marker.
- Anti-Vimentin antibody Vimentin is an intermediate filament characteristic of mesenchymal cells. Marker of mesenchymal cells.
- Anti-N-cadherin antibody A process in which epithelial cells differentiate into mesenchymal cells and expresses N-cadherin.
- CTGF connective tissue growth factor
- Anti- ⁇ -SMA antibody The process of differentiation of epithelial cells into mesenchymal cells and expressing ⁇ -SMA. Marker of epithelial-mesenchymal transition.
- the results of immunostaining are shown in FIG. In FIG. 9, the scale bar of the immunostained image with anti-CK AE1 / AE3 antibody, anti-vimentin antibody and anti-N-cadherin antibody indicates 50 ⁇ m.
- the scale bar of the immunostained image with anti-CTGF antibody and anti- ⁇ -SMA indicates 100 ⁇ m. Further, in the immunostained image with the anti- ⁇ -SMA antibody in FIG.
- FIG. 9 shows that at the 40th day after the induction of peritonitis, the CXM group had suppressed the appearance of vimentin positive cells, N-cadherin positive cells and ⁇ -SMA positive cells compared to the CG group. This means that the epithelial-mesenchymal transition of mesothelial cells and the appearance of myofibroblasts, which cause peritoneal fibrosis, were suppressed.
- FIGS. 10B to 10D the number of CD45 positive cells, the number of F4 / 80 positive cells, and the ratio of PCNA positive cells in the mouse subepithelial interstitial layer (SMIL) were calculated. Were graphed (see FIGS. 10B to 10D). In FIG. 10B and FIG. 10C, the number of each positive cell is represented by area (mm 2 ), and in FIG. 10D, the ratio of the area of PCNA positive cell to the total area of SMIL (%) is represented.
- the CXM group showed the appearance of CD45 positive leukocytes, F4 / 80 positive macrophages and PCNA positive mesenchymal cells compared to the CG group. It was significantly suppressed. From these results, it was suggested that peritoneal fibrosis was suppressed by suppressing peritonitis in the CMX group.
- the dried filamentous atelocollagen vitrigel suppressed peritoneal inflammation and fibrosis caused by chlorhexidine.
- gel-like collagen similar peritoneal inflammation-suppressing effect and fibrosis-suppressing effect were observed, but a significant difference was observed in the effect between dried filamentous atelocollagen vitrigel and gel-like collagen. That is, the dried filamentous atelocollagen vitrigel had significantly superior peritoneal inflammation suppression effect and fibrosis suppression effect than the gel collagen.
- no significant change was observed in the properties of the dried filamentous atelocollagen vitrigel (see FIGS. 8A to 8C). From this, it was guessed that the peritoneal fibrosis inhibitory effect continues after this.
- a yarn having excellent strength can be manufactured.
- yarn obtained by the said manufacturing method consists of an atelocollagen vitrigel dried body, it is the structure where the atelocollagen vitrigel dried body converged with high density, and has the epithelialization promotion effect and scar formation suppression effect. Therefore, the yarn is useful as a tissue regeneration yarn.
- the yarn obtained by the production method has good cell adhesion and proliferation. Therefore, it is useful as a carrier for cell transplantation.
- the yarn obtained by the production method has an inhibitory action on inflammation and fibrosis of the wall side peritoneum and visceral peritoneum. In addition, it has an inhibitory action on the adhesion of the visceral peritoneum (intestinal tract). Therefore, it is useful as a peritonitis inhibitor, a peritoneal fibrosis inhibitor, or an intestinal adhesion inhibitor.
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Abstract
Description
本願は、2017年5月18日に、日本に出願された特願2017-098931号に基づき優先権を主張し、その内容をここに援用する。
本発明の第1態様に係る糸の製造方法は、
柱状ハイドロゲルに紫外線を照射する工程Aと、
前記紫外線照射後の柱状ハイドロゲルをガラス化して、糸状ハイドロゲル乾燥体を得る工程Bと、
前記糸状ハイドロゲル乾燥体を再水和して、糸状ビトリゲルを得る工程Cと、
をこの順に備える方法である。
上記第1態様に係る糸の製造方法において、前記工程Cの後、さらに、前記糸状ビトリゲルを再ガラス化して、糸状ビトリゲル乾燥体を得る工程Dを備えてもよい。
上記第1態様に係る糸の製造方法において、前記工程Dの後、前記糸状ビトリゲル乾燥体に紫外線を再照射する工程Eを備えてもよい。
上記第1態様に係る糸の製造方法において、前記工程Eの後、さらに、紫外線を再照射された前記糸状ビトリゲル乾燥体に疎水性溶媒を付着又は含浸させる工程Fを備えてもよい。
上記第1態様に係る糸の製造方法において、前記ハイドロゲルが、アテロコラーゲンゲルであってもよい。
上記第1態様に係る糸の製造方法において、前記糸は、縫合糸として使用可能な組織再生糸であってもよい。
上記第1態様に係る糸の製造方法において、前記糸は、細胞移植用担体であってもよい。
上記第1態様に係る糸の製造方法において、前記糸は、結膜瘻孔部の補填材であってもよい。
上記第1態様に係る糸の製造方法において、前記糸は、腹膜炎抑制剤又は腹膜線維化抑制剤であってもよい。
前記糸の破断強度が0.1kgf以上であってもよい。
前記糸の破断強度が0.2kgf以上であってもよい。
前記ビトリゲル乾燥体がアテロコラーゲンビトリゲル乾燥体であってもよい。
前記疎水性溶媒がシリコンオイルであってもよい。
前記糸は、縫合糸として使用可能な組織再生糸であってもよい。
前記糸は、細胞移植用担体であってもよい。
前記糸は、結膜瘻孔部の補填材であってもよい。
前記糸は、腹膜炎抑制剤又は腹膜線維化抑制剤であってもよい。
<第1実施形態>
本発明の第1実施形態に係る糸の製造方法は、
柱状ハイドロゲルに紫外線を照射する工程Aと、
前記紫外線照射後の柱状ハイドロゲルをガラス化して、糸状ハイドロゲル乾燥体を得る工程Bと、
前記糸状ハイドロゲル乾燥体を再水和して、糸状ビトリゲルを得る工程Cと、
をこの順に備える方法である。
これに対し、本実施形態の製造方法によれば、ネイティブコラーゲンゲルよりも強度のないハイドロゲルを原料としても、糸を製造することができる。
以下、本実施形態の糸の製造方法の各工程について、詳細を説明する。
まず、柱状ハイドロゲルに紫外線を照射し、柱状ハイドロゲルの強度を上げる。
工程Aで用いられる柱状ハイドロゲルは、例えば、ゾルを所望の径となるように筒状の型等を用いて、ゲル化させて得られたものであればよい。また、ゲル化する際にゾルを保温する温度は、用いるゾルの種類に応じて適宜調整すればよい。例えば、ゾルがコラーゲンゾルである場合、ゲル化する際の保温は、用いるコラーゲンの動物種に依存したコラーゲンの変性温度より低い温度とすればよく、一般的には20℃以上37℃以下の温度で保温することで数分から数時間でゲル化を行うことができる。
また、「ビトリゲル」とは、従来のハイドロゲルをガラス化(vitrification)した後に再水和して得られる安定した状態にあるゲルのことを指し、本発明者によって、「ビトリゲル(vitrigel)(登録商標)」と命名されている。
また、本明細書においては、本実施形態の製造工程を詳細に説明するにあたり、当該ガラス化工程の直後であり再水和の工程を経ていないハイドロゲルの乾燥体に対しては、単に「ハイドロゲル乾燥体」とした。そして、当該ガラス化工程の後に再水和の工程を経て得られたゲルを「ビトリゲル」として区別して表し、そのビトリゲルをガラス化させて得られた乾燥体を「ビトリゲル乾燥体」とした。また、ビトリゲル乾燥体に紫外線照射する工程を施して得られるものを「紫外線を再照射された糸状ビトリゲル乾燥体」とした。従って、「ビトリゲル」は水和体である。
前記ゲル化する細胞外マトリックス由来成分としては、例えば、コラーゲン(I型、II型、III型、V型、XI型等)、マウスEHS腫瘍抽出物(IV型コラーゲン、ラミニン、ヘパラン硫酸プロテオグリカン等を含む)より再構成された基底膜成分(商品名:マトリゲル)、グリコサミノグリカン、ヒアルロン酸、プロテオグリカン、ゼラチン等が挙げられ、これらに限定されない。それぞれのゲル化に至適な塩等の成分、その濃度、pH等を選択し所望のビトリゲルを製造することが可能である。また、原料を組み合わせることで、様々な生体内組織を模倣したビトリゲルを得ることができる。
中でも、ゾルとしては、ゲル化する細胞外マトリックス由来成分が好ましく、コラーゲンがより好ましい。また、コラーゲンの中でもより好ましい原料としては、ネイティブコラーゲン又はアテロコラーゲンを例示でき、アテロコラーゲンがさらに好ましい。すなわち、本工程において用いられるハイドロゲルとしては、創傷部における上皮化促進効果及び瘢痕形成抑制効果を有する生体適合性素材であることから、アテロコラーゲンゲルが特に好ましい。
また、上記例示されたゾルから得られるハイドロゲルは、その組成及び含有量によっては、ネイティブコラーゲンゲルと同等の強度を有するゲル、又は、ネイティブコラーゲンゲルよりも強度のないゲルとなる。また、ネイティブコラーゲンゲルよりも強度のあるゲルとなってもよい。いずれの強度のハイドロゲルであっても、本実施形態の製造方法によれば、上記例示されたゾルから得られるハイドロゲルを原料として、糸を製造することができる。
また、「瘢痕形成抑制効果」とは、創傷部が治癒した後に残る痕(瘢痕)、いわゆる傷痕が形成されることを抑制する効果を意味する。アテロコラーゲンビトリゲル乾燥体からなる糸を縫合糸として使用することで、傷痕を残さずに創傷部を治療することができる。
また、柱状ハイドロゲルへの紫外線の照射は、柱状ハイドロゲルの全面に紫外線が照射されるように、紫外線の照射部位を、柱状ハイドロゲルの一方の面と他方の面と(例えば、「上面と下面と」、又は、「表面と裏面と」等)に分けて照射して、その総照射量を、柱状ハイドロゲルへの単位面積あたりの紫外線総照射量としてもよい。
次いで、紫外線照射後の柱状ハイドロゲルを乾燥し、ガラス化させることで、糸状ハイドロゲル乾燥体を得る。
柱状ハイドロゲルを乾燥させることにより、柱状ハイドロゲル内の自由水を完全に除去し、さらに結合水の部分除去を進行させることができる。
このガラス化工程(柱状ハイドロゲル内の自由水を完全に除去した後に、結合水の部分除去を進行させる工程)の期間を長くするほど、再水和した際には透明度、強度に優れた糸状ビトリゲルを得ることができる。なお、必要に応じて短期間のガラス化後に再水和して得た糸状ビトリゲルをPBS等で洗浄し、再度ガラス化することもできる。
また、本工程において、上述の工程Aで紫外線を照射させたことで、柱状ハイドロゲルは適度な強度を有するため、乾燥の際に、物干し等に吊り下げた状態で効率的に乾燥させることができる。
次いで、得られた糸状ハイドロゲル乾燥体を再水和して糸状ビトリゲルを得る。
このとき、生理食塩水、PBS(Phosphate Buffered Saline)等を用いて、再水和させればよい。
本発明の第2実施形態に係る糸の製造方法は、前記工程Cの後、さらに、前記糸状ビトリゲルを再ガラス化して、糸状ビトリゲル乾燥体を得る工程Dを備える方法である。
工程A~工程Cについては、上述の第1実施形態に記載のとおりである。本実施形態における工程Dについて、以下に詳細を説明する。
次いで、得られた糸状ビトリゲルを乾燥し、再度ガラス化する。
乾燥方法としては、上記工程Bで例示された方法と同様の方法が挙げられる。
また、本工程において、糸状ビトリゲルは適度な強度を有するため、乾燥の際に、物干し等に吊り下げた状態で効率的に乾燥させることができる。
本発明の第3実施形態に係る糸の製造方法は、前記工程Dの後、さらに、前記糸状ビトリゲル乾燥体に紫外線を再照射する工程Eを備える方法である。
工程A~工程Dについては、上述の第1実施形態及び第2実施形態に記載のとおりである。本実施形態における工程Eについて、以下に詳細を説明する。
次いで、得られた糸状ビトリゲル乾燥体に紫外線を再照射して、糸状ビトリゲル乾燥体の強度をさらに上げる。
また、糸状ビトリゲル乾燥体への紫外線の照射は、糸状ビトリゲル乾燥体の全面に紫外線が照射されるように、紫外線の照射部位を、糸状ビトリゲル乾燥体の一方の面と他方の面と(例えば、「上面と下面と」、又は、「表面と裏面と」等)に分けて照射して、その総照射量を、糸状ビトリゲル乾燥体への単位面積あたりの紫外線総照射量としてもよい。
本発明の第4実施形態に係る糸の製造方法は、前記工程Eの後、さらに、紫外線が再照射された前記糸状ビトリゲル乾燥体に疎水性溶媒を付着又は含浸させる工程Fを備える方法である。
工程A~工程Eについては、上述の第1実施形態、第2実施形態及び第3実施形態に記載のとおりである。本実施形態における工程Fについて、以下に詳細を説明する。
次いで、紫外線再照射後の糸状ビトリゲル乾燥体に疎水性溶媒を付着又は含浸させる。これにより、糸状ビトリゲル乾燥体のしなやかさが増して、縫合糸等の用途で用いる際に、疎水性溶媒が潤滑剤として働き、裂傷部をひっかかりなく、なめらかに縫合することができる。また、疎水性溶媒を糸状ビトリゲル乾燥体の表面上に付着させる、又は、表面直下から内部へと含侵させることで、縫合部において体液等による再水和による強度の低下が防止され、糸の強度が維持される。
なお、ここでいう「付着させる」とは、疎水性溶媒を糸状ビトリゲル乾燥体の表面にくっつかせることを意味し、「含浸させる」とは疎水性溶媒を糸状ビトリゲル乾燥体の表面直下から内部へと染み込ませることを意味する。
中でも、疎水性溶媒としては、シリコンオイルであることが好ましい。シリコンオイルは変性されていないものであってもよく、変性されたものであってもよい。シリコンオイルとしてより具体的には、例えば、ポリジメチルシロキサン、ポリメチルフェニルシロキサン、ポリジフェニルシロキサン、ポリメチルハイドロジェンシロキサン等が挙げられ、これらに限定されない。
疎水性溶媒を付着又は含浸させる時間は、特別な限定はなく、例えば30分以上48時間以下であればよい。
疎水性溶媒を付着又は含浸させる方法としては、例えば、疎水性溶媒に糸状ビトリゲル乾燥体を浸漬させる方法、糸状ビトリゲル乾燥体に疎水性溶媒を塗布する方法、糸状ビトリゲル乾燥体に疎水性溶媒を噴霧する方法等が挙げられ、これらに限定されない。
本実施形態の製造方法により得られた糸は、後述の実施例に示すとおり、例えば、組織再生糸、細胞移植用担体等として用いることができる。又は、本実施形態の製造方法により得られた糸は、後述の実施例に示すとおり、硝子体手術の際に治療機器を硝子体内に挿入するために作製する結膜瘻孔部の補填材として用いることができる。又は、本実施形態の製造方法により得られた糸は、後述の実施例に示すとおり、腹腔内へ挿入して腹膜炎及び腹膜線維化を抑制する留置材として用いることができる。
本発明の一実施形態に係る糸は、ビトリゲル乾燥体からなり、疎水性溶媒が付着又は含浸されている。
本実施形態の糸の横断面の形状は、特別な限定はなく、例えば、三角形、四角形(正方形、長方形、台形含む)、五角形、六角形、七角形、八角形等の多角形;円形、楕円形、略円形、楕円形、略楕円形、半円形、扇形等が挙げられ、これらに限定されない。中でも、糸の横断面の形状は、円形であることが好ましい。
また、本実施形態の糸の横断面の形状が円形である場合、その平均直径は、用途に応じて適宜選択すればよい。糸の平均直径としては、例えば1μm以上1mm以下であればよく、例えば3μm以上900μm以下であればよい。
なお、糸の破断強度の測定方法は、以下のとおりである。
デジタルフォースゲージ(日本電産シンポ社製)を使用して、糸を全長5cmに切断した後に両端の1cmを固定して、毎分9mmで引っ張った時の破断強度(kgf)を測定すればよい。
次いで、本実施形態の糸の構成成分について、以下に詳細を説明する。
本実施形態の糸は、ビトリゲル乾燥体からなる。
ビトリゲル乾燥体の原料となるゾルとしては、上述の糸の製造方法において例示されたものと同様のものが挙げられる。中でも、本実施形態の糸を構成するビトリゲル乾燥体としては、創傷部における上皮化促進効果及び瘢痕形成抑制効果を有する生体適合性素材であることから、アテロコラーゲンビトリゲル乾燥体であることが好ましい。
本実施形態の糸は、疎水性溶媒が付着又は含浸されている。
疎水性溶媒としては、上述の糸の製造方法において例示されたものと同様のものが挙げられる。中でも、本実施形態の糸に含まれる疎水性溶媒としては、シリコンオイルであることが好ましい。
本実施形態の糸は、後述の実施例において示すとおり、優れた強度を有し、且つ、体液等が存在してもその強度が維持されることから縫合糸として有用である。さらに、本実施形態の糸を縫合糸として使用した場合に、創傷部において組織の再生が促進され、且つ、瘢痕が形成されない。すなわち、本実施形態の糸は、縫合糸として使用可能な組織再生糸として有用である。
特に、本実施形態の糸が、アテロコラーゲンビトリゲル乾燥体で構成される場合、創傷部における上皮化促進効果及び瘢痕形成抑制効果を有することから、組織再生糸として好適である。
なお、本明細書において、「組織再生糸」とは、縫合部における組織の再生を促進する糸を意味する。ここで、「組織の再生の促進」とは、具体的には、創傷部の治癒過程における創収縮の促進、肉芽組織の形成抑制、表皮細胞の増殖による再生上皮の形成促進等を示す。
(1)柱状アテロコラーゲンゲルの調製
まず、1.0%ブタアテロコラーゲン溶液(関東化学社製)と無血清培養液とを等量混和した0.5%のブタ由来アテロコラーゲン溶液を調製した。次いで、調製したアテロコラーゲン溶液を1mLピペット内に1.4mL、5mLピペット内に7mL、それぞれ吸い込ませた。次いで、各ピペットの両端をパラフィルムで密閉し、細胞培養用インキュベーター(37℃、5%CO2)内で2時間静置し、ゲル化させて、柱状アテロコラーゲンゲルを調製した。
次いで、各ピペットの両端からパラフィルムを除去した。ピペット内から柱状アテロコラーゲンゲルを取り出し、ビニールシートが敷かれた平面状のトレイの上に直線的に張った状態で静置した。次いで、紫外線を照射し(照射エネルギー:800mJ/cm2)、柱状アテロコラーゲンゲルを反転させて、再度紫外線を照射した(照射エネルギー:800mJ/cm2)。合計の紫外線照射エネルギーは、1600mJ/cm2であった。
次いで、紫外線が照射された柱状アテロコラーゲンゲルの一端をポリプロピレン樹脂製の物干しの縁に固定して吊るした。次いで、温度10℃、湿度40%の条件の恒温恒湿機を備えた簡易クリーンベンチ内で、充分に風乾して、吊るされた状態の柱状アテロコラーゲンゲルをガラス化させて、糸状アテロコラーゲンゲル乾燥体を調製した。
次いで、得られた糸状アテロコラーゲンゲル乾燥体をPBSで再水和し、糸状アテロコラーゲンビトリゲルを調製した。
次いで、得られた糸状アテロコラーゲンビトリゲルの一端をポリプロピレン樹脂製の物干しの縁に固定して吊るした。次いで、温度10℃、湿度40%の条件の恒温恒湿機を備えた簡易クリーンベンチ内で、充分に風乾して、吊るされた状態の糸状アテロコラーゲンゲルを再ガラス化させて、糸状アテロコラーゲンビトリゲル乾燥体を調製した。
次いで、得られた糸状アテロコラーゲンビトリゲル乾燥体を平面状のトレイの上に直線的に張った状態で静置した。次いで、紫外線を照射し(照射エネルギー:400mJ/cm2)、糸状アテロコラーゲンゲルを反転させて、再度紫外線を照射した(照射エネルギー:400mJ/cm2)。合計の紫外線照射エネルギーは、800mJ/cm2であった。
得られた紫外線照射後の糸状アテロコラーゲンビトリゲル乾燥体の平均直径について、1mLのピペットを用いて製造されたもの(以下、「糸状アテロコラーゲンビトリゲル乾燥体1」と称する場合がある)は、148±42μmであり、5mLのピペットを用いて製造されたもの(以下、「糸状アテロコラーゲンビトリゲル乾燥体2」と称する場合がある)は、444±30μmであった。
製造例1で製造された糸状アテロコラーゲンビトリゲル乾燥体1及び糸状アテロコラーゲンビトリゲル乾燥体2の破断強度を測定した。
測定対象として、糸状アテロコラーゲンビトリゲル乾燥体1(以下、「乾燥体1」と称する場合がある)、乾燥体1を再水和した糸状アテロコラーゲンビトリゲル(以下、「再水和体1」と称する場合がある)、シリコンオイルを浸潤させた糸状アテロコラーゲンビトリゲル乾燥体1(以下、「浸潤体1」と称する場合がある)、糸状アテロコラーゲンビトリゲル乾燥体2(以下、「乾燥体2」と称する場合がある)、乾燥体2を再水和した糸状アテロコラーゲンビトリゲル(以下、「再水和体2」と称する場合がある)及びシリコンオイルを浸潤させた糸状アテロコラーゲンビトリゲル乾燥体2(以下、「浸潤体2」と称する場合がある)を準備した。
また、対照として、ポリグラクチン縫合糸バイクリル(登録商標)(7-0、縫合糸の規格の平均直径:50~69μm程度)(以下、「乾燥体3」と称する場合がある)、乾燥体3を再水和したバイクリル(登録商標)(以下、「再水和体3」と称する場合がある)及びシリコンオイルを浸潤させたバイクリル(登録商標)(以下、「浸潤体3」と称する場合がある)も準備した。
図1Aは、各条件の糸状アテロコラーゲンビトリゲル乾燥体1における破断強度、図1Bは各条件の糸状アテロコラーゲンビトリゲル乾燥体2における破断強度、及び、図1Cは各条件のポリグラクチン縫合糸バイクリル(登録商標)における破断強度を示したものである。
また、乾燥体2及び浸潤体2は破断強度が1kgfよりも大きく、対照であるバイクリル(登録商標)の乾燥体3、再水和体3及び浸潤体3よりも優れた強度を有することが確かめられた。これは、平均直径の大きさに由来するものであると推察された。
製造例1で得られた糸状アテロコラーゲンビトリゲル乾燥体1をシリコンオイルで浸潤させたもの(浸潤体1)が手術用に耐えうる強度であることを確かめるために、マウス表皮切開部の縫合試験を行った。縫合を行った当日のマウスの画像を図2に示す。
さらに、対照としてポリグラクチン縫合糸バイクリル(登録商標)(7-0、縫合糸の規格の平均直径:50~69μm程度)(乾燥体3)を用いてマウス表皮切開部の縫合試験を行った。浸潤体1を用いた場合と同様に、縫合7日目の縫合部の組織切片を作製し、HE染色及び抗α-SMA抗体を用いた免疫染色を行った。HE染色の結果を図3Bに、抗α-SMA抗体による免疫染色による結果を図3Dに示す。
さらに、図3C及び図3Dから、乾燥体3を用いた場合と比較して、浸潤体1を用いた場合では、瘢痕形成の主体となるαSMA陽性の筋線維芽細胞数が、縫合部周囲で圧倒的に少ないことが明らかとなった。
製造例1で得られた糸状アテロコラーゲンビトリゲル乾燥体2(乾燥体2)が優れた強度を有することを確かめるために、ブタの結膜欠損部(瘻孔部)に補填材として使用した。補填材として埋め込んだ当日のブタの結膜瘻孔部の画像を図4Aに示す。図4Aにおいて、矢印は、埋め込まれた乾燥体2を示す。
また、対照として、通常、結膜瘻孔部の補填材として用いられるプラスチックポートを埋め込んだ。その結果を図4Bに示す。図4Bにおいて、矢印は、埋め込まれたプラスチックポートを示す。
製造例1で糸状アテロコラーゲンビトリゲル乾燥体1を再水和したもの(再水和体1)が良好な細胞接着性及び増殖性を有することを確かめるために、内皮細胞及び線維芽細胞を用いた細胞培養試験を行った。
具体的には、内皮細胞(MS-1、ATCC(American Type Culture Collection))及び線維芽細胞(Wistar rat由来初代培養真皮線維芽細胞)をそれぞれ、5cmに切断した再水和体1とともにシャーレで10日間培養した。培養後、再水和体1を取り出し、HE染色を行い、光学顕微鏡(OLYMPUS社製、BX53)を用いて観察した。図5Aは、内皮細胞と共に培養した再水和体1を示す画像であり、図5Bは線維芽細胞と共に培養した再水和体1を示す画像である。図5Aにおいて、矢印は、再水和体1に接着した内皮細胞を示す。
また、図5A及び図5Bから、再水和させた糸状アテロコラーゲンビトリゲルは、内皮細胞及び線維芽細胞共に良好な接着性及び増殖性を示すことが確認された。
製造例1で製造された糸状アテロコラーゲンビトリゲル乾燥体1及び糸状アテロコラーゲンビトリゲル乾燥体2を腹膜線維化モデルマウスに留置することによる影響を調べた。
図6Aは、製造例1で製造された糸状アテロコラーゲンビトリゲル乾燥体1及び糸状アテロコラーゲンビトリゲル乾燥体2を示す画像である。図6Aにおいて、「CXM1」は糸状アテロコラーゲンビトリゲル乾燥体1を示し、「CXM5」は糸状アテロコラーゲンビトリゲル乾燥体2を示す。また、図6Bは、糸状アテロコラーゲンビトリゲル乾燥体のマウス腹腔内への挿入方法を示す図である。
体重40gの雌のICRマウスの腹腔内に、留置針及びピンセットを用いて、糸状アテロコラーゲンビトリゲル乾燥体1及び糸状アテロコラーゲンビトリゲル乾燥体2をそれぞれ挿入し、留置した(図6C参照)。
糸状アテロコラーゲンビトリゲル乾燥体を留置させた翌日に、当該マウスの腹腔内に0.1%のクロルヘキシジン溶液(15%エタノール含有生理食塩水溶液を用いて予め調製)を体重1kg当たり10mLの投与量で、1日おきに投与した。
なお、対照試験群も含め、以下の4群を準備した。
Sham群:針穿刺のみ、クロルヘキシジン腹腔内注射なし
CG群:クロルヘキシジン腹腔内注射のみ
Gel群:アテロコラーゲンゲル腹腔内注入、クロルヘキシジン腹腔内注射あり
CXM群:糸状アテロコラーゲンビトリゲル乾燥体腹腔内挿入、クロルヘキシジン腹腔内注射あり
腹膜炎誘導後40日目及び56日目に、各群のマウス1匹ずつを開腹し、目視により観察した。結果を図7A(腹膜炎誘導後40日目)及び図8A(腹膜炎誘導後56日目)に示す。図7Aにおいて、CG群及びGel群に記載の矢頭は、腹膜と腸管との癒着を示し、Gel群に記載の矢印は腹膜に留置されたコラーゲンゲルを示し、CXM群に記載の矢印は腹膜に留置された糸状アテロコラーゲンビトリゲルを示す。また、図8Aにおいて、CG群に記載の矢頭は、腹膜と腸管との癒着を示し、CXM群に記載の矢印は腹膜に留置された糸状アテロコラーゲンビトリゲルを示す。
次いで、腹膜炎誘導後40日目及び56日目の各群のマウスの腹膜の組織切片を作製し、HE染色及びアザン染色を行った。腹膜炎誘導後40日目の各群のマウスにおける結果を図7B(HE染色像)及び図7C(アザン染色像)に示す。また、腹膜炎誘導後56日目の各群のマウスにおける結果を図8B(HE染色像)及び図8C(アザン染色像)に示す。
図7B及び図8Bにおいて、上図は壁側腹膜のHE染色像であり、下図は臓側腹膜のHE染色像である。スケールバーは100μmを示す。また、図7C及び図8Cにおいて、スケールバーは200μmを示す。
さらに、図7C及び図8Cそれぞれに示すアザン染色像から、各群のマウスの中皮下結合織の厚さ(μm)を測定し、その平均値をグラフ化した(図7D及び図8D参照)。
また、図8A~図8Dから、腹膜炎誘導後56日目の時点で、CMX群は、CG群と比較して、壁側腹膜の線維化が有意に抑制されていた。また、これ以降は、CG群の体重減少が著しく、試験の継続が不能であった。
次いで、腹膜炎誘導後40日目の各群のマウスの腹膜の組織切片を作製し、各種抗体を用いて免疫染色を行った。用いた抗体を以下に示す。
抗サイトケラチンAE1/AE3(CK AE1/AE3)抗体:CK AE1/AE3は、汎用の上皮性マーカーである。
抗ビメンチン(Vimentin)抗体:ビメンチンは、間葉系細胞に特有の中間径フィラメントである。間葉系細胞のマーカー。
抗N-カドヘリン(N-cadherin)抗体:上皮細胞が間葉系細胞へと分化するプロセスで、N-カドヘリンを発現する。上皮-間葉分化転換のマーカー。
抗結合組織成長因子(connective tissue growth factor:CTGF)抗体:CTGFは、線維芽細胞の増殖とコラーゲンの産生を冗進させる因子である。線維化マーカー。
抗α-SMA抗体:上皮細胞が間葉系細胞へと分化するプロセスで、α-SMAを発現する。上皮-間葉分化転換のマーカー。
また、免疫染色の結果を図9に示す。図9において、抗CK AE1/AE3抗体、抗ビメンチン抗体及び抗N-カドヘリン抗体による免疫染色像のスケールバーは50μmを示す。抗CTGF抗体及び抗α-SMAによる免疫染色像のスケールバーは100μmを示す。また、図9の抗α-SMA抗体による免疫染色像において、矢頭は、陽性コントロールとなる血管壁を示す。
次いで、腹膜炎誘導後40日目の各群のマウスの腹膜の組織切片を作製し、各種抗体を用いて免疫染色を行った。用いた抗体を以下に示す。
抗CD45抗体:CD45は、白血球のマーカーである。
抗F4/80抗体:F4/80は、マウスの成熟マクロファージのマーカーである。
抗増殖細胞核抗原(proliferating cell nuclear antigen:PCNA)抗体:PCNAは、細胞周期関連核タンパク質である。細胞増殖と細胞周期とのマーカー(G1~S期)。
また、免疫染色の結果を図10Aに示す。図10Aにおいて、スケールバーは50μmを示す。
さらに、図10Aの各免疫染色像から、マウスの中皮下間質層(submesothelial interstitial layer:SMIL)中のCD45陽性細胞の数、F4/80陽性細胞の数及びPCNA陽性細胞の割合を算出して、グラフ化した(図10B~図10D参照)。なお、図10B及び図10Cでは、各陽性細胞の数を面積(mm2)で表し、図10Dでは、SMIL全体の面積に対するPCNA陽性細胞の面積の割合(%)で表した。
また、腹膜炎誘導後56日目でも、糸状アテロコラーゲンビトリゲル乾燥体の性状に大きな変化が見られなかった(図8A~図8C参照)。このことから、これ以降も腹膜線維化抑制効果は継続するものと推察された。
Claims (18)
- 柱状ハイドロゲルに紫外線を照射する工程Aと、
前記紫外線照射後の柱状ハイドロゲルをガラス化して、糸状ハイドロゲル乾燥体を得る工程Bと、
前記糸状ハイドロゲル乾燥体を再水和して、糸状ビトリゲルを得る工程Cと、
をこの順に備える糸の製造方法。 - 前記工程Cの後、さらに、前記糸状ビトリゲルを再ガラス化して、糸状ビトリゲル乾燥体を得る工程Dを備える請求項1に記載の糸の製造方法。
- 前記工程Dの後、さらに、前記糸状ビトリゲル乾燥体に紫外線を再照射する工程Eを備える請求項1又は2に記載の糸の製造方法。
- 前記工程Eの後、さらに、紫外線を再照射された前記糸状ビトリゲル乾燥体に疎水性溶媒を付着又は含浸させる工程Fを備える請求項1~3のいずれか一項に記載の糸の製造方法。
- 前記ハイドロゲルが、アテロコラーゲンゲルである請求項1~4のいずれか一項に記載の糸の製造方法。
- 前記糸は、縫合糸として使用可能な組織再生糸である請求項1~5のいずれか一項に記載の糸の製造方法。
- 前記糸は、細胞移植用担体である請求項1~5のいずれか一項に記載の糸の製造方法。
- 前記糸は、結膜瘻孔部の補填材である請求項1~7のいずれか一項に記載の糸の製造方法。
- 前記糸は、腹膜炎抑制剤又は腹膜線維化抑制剤である請求項1~5のいずれか一項に記載の糸の製造方法。
- ビトリゲル乾燥体からなり、疎水性溶媒が付着又は含浸された糸。
- 前記糸の破断強度が0.1kgf以上である請求項10に記載の糸。
- 前記糸の破断強度が0.2kgf以上である請求項10又は11に記載の糸。
- 前記ビトリゲル乾燥体がアテロコラーゲンビトリゲル乾燥体である請求項10~12のいずれか一項に記載の糸。
- 前記疎水性溶媒がシリコンオイルである請求項10~13のいずれか一項に記載の糸。
- 前記糸は、縫合糸として使用可能な組織再生糸である請求項10~14のいずれか一項に記載の糸。
- 前記糸は、細胞移植用担体である請求項10~14のいずれか一項に記載の糸。
- 前記糸は、結膜瘻孔部の補填材である請求項10~16のいずれか一項に記載の糸。
- 前記糸は、腹膜炎抑制剤又は腹膜線維化抑制剤である請求項10~14のいずれか一項に記載の糸。
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WO2020230643A1 (ja) * | 2019-05-13 | 2020-11-19 | 国立研究開発法人農業・食品産業技術総合研究機構 | 糸及びその製造方法 |
JP2021038502A (ja) * | 2020-11-26 | 2021-03-11 | 国立研究開発法人農業・食品産業技術総合研究機構 | 糸及びその製造方法 |
WO2021090617A1 (ja) * | 2019-11-05 | 2021-05-14 | 国立研究開発法人農業・食品産業技術総合研究機構 | ハイドロゲル膜乾燥体又はビトリゲル膜乾燥体、その製造装置及びその製造方法、並びに、鼓膜治療デバイス及び創部治療デバイス |
WO2022085377A1 (ja) * | 2020-10-19 | 2022-04-28 | 国立研究開発法人農業・食品産業技術総合研究機構 | 複合糸及びその使用 |
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