WO2014175301A1 - 人工血管 - Google Patents
人工血管 Download PDFInfo
- Publication number
- WO2014175301A1 WO2014175301A1 PCT/JP2014/061362 JP2014061362W WO2014175301A1 WO 2014175301 A1 WO2014175301 A1 WO 2014175301A1 JP 2014061362 W JP2014061362 W JP 2014061362W WO 2014175301 A1 WO2014175301 A1 WO 2014175301A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- blood vessel
- artificial blood
- dtex
- multifilament yarn
- less
- Prior art date
Links
- 210000004204 blood vessel Anatomy 0.000 title claims abstract description 121
- 239000002473 artificial blood Substances 0.000 title claims abstract description 113
- 239000000835 fiber Substances 0.000 claims abstract description 66
- 239000004744 fabric Substances 0.000 claims abstract description 24
- 229920000728 polyester Polymers 0.000 claims abstract description 11
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 39
- 239000002759 woven fabric Substances 0.000 claims description 33
- 230000035699 permeability Effects 0.000 claims description 32
- 239000003146 anticoagulant agent Substances 0.000 claims description 9
- 230000002785 anti-thrombosis Effects 0.000 claims description 7
- 230000001788 irregular Effects 0.000 claims description 6
- 239000000463 material Substances 0.000 claims description 5
- 208000007536 Thrombosis Diseases 0.000 abstract description 12
- 230000015572 biosynthetic process Effects 0.000 abstract description 6
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- 238000000034 method Methods 0.000 description 39
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- 239000008280 blood Substances 0.000 description 7
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- HEMHJVSKTPXQMS-UHFFFAOYSA-M Sodium hydroxide Chemical compound [OH-].[Na+] HEMHJVSKTPXQMS-UHFFFAOYSA-M 0.000 description 6
- 239000000126 substance Substances 0.000 description 6
- 229940079593 drug Drugs 0.000 description 5
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- 210000002889 endothelial cell Anatomy 0.000 description 5
- 230000014759 maintenance of location Effects 0.000 description 5
- 229920000669 heparin Polymers 0.000 description 4
- 150000002500 ions Chemical class 0.000 description 4
- 238000004519 manufacturing process Methods 0.000 description 4
- 229920000139 polyethylene terephthalate Polymers 0.000 description 4
- 239000005020 polyethylene terephthalate Substances 0.000 description 4
- 229910001220 stainless steel Inorganic materials 0.000 description 4
- HTTJABKRGRZYRN-UHFFFAOYSA-N Heparin Chemical compound OC1C(NC(=O)C)C(O)OC(COS(O)(=O)=O)C1OC1C(OS(O)(=O)=O)C(O)C(OC2C(C(OS(O)(=O)=O)C(OC3C(C(O)C(O)C(O3)C(O)=O)OS(O)(=O)=O)C(CO)O2)NS(O)(=O)=O)C(C(O)=O)O1 HTTJABKRGRZYRN-UHFFFAOYSA-N 0.000 description 3
- OKKJLVBELUTLKV-UHFFFAOYSA-N Methanol Chemical compound OC OKKJLVBELUTLKV-UHFFFAOYSA-N 0.000 description 3
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- WNLRTRBMVRJNCN-UHFFFAOYSA-N adipic acid Chemical compound OC(=O)CCCCC(O)=O WNLRTRBMVRJNCN-UHFFFAOYSA-N 0.000 description 2
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- QQVIHTHCMHWDBS-UHFFFAOYSA-N isophthalic acid Chemical compound OC(=O)C1=CC=CC(C(O)=O)=C1 QQVIHTHCMHWDBS-UHFFFAOYSA-N 0.000 description 2
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- 229920001707 polybutylene terephthalate Polymers 0.000 description 2
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- 239000010935 stainless steel Substances 0.000 description 2
- LMDZBCPBFSXMTL-UHFFFAOYSA-N 1-ethyl-3-(3-dimethylaminopropyl)carbodiimide Chemical compound CCN=C=NCCCN(C)C LMDZBCPBFSXMTL-UHFFFAOYSA-N 0.000 description 1
- BSYNRYMUTXBXSQ-FOQJRBATSA-N 59096-14-9 Chemical compound CC(=O)OC1=CC=CC=C1[14C](O)=O BSYNRYMUTXBXSQ-FOQJRBATSA-N 0.000 description 1
- 239000005528 B01AC05 - Ticlopidine Substances 0.000 description 1
- 241000283690 Bos taurus Species 0.000 description 1
- 102000008186 Collagen Human genes 0.000 description 1
- 108010035532 Collagen Proteins 0.000 description 1
- 102000009123 Fibrin Human genes 0.000 description 1
- 108010073385 Fibrin Proteins 0.000 description 1
- BWGVNKXGVNDBDI-UHFFFAOYSA-N Fibrin monomer Chemical compound CNC(=O)CNC(=O)CN BWGVNKXGVNDBDI-UHFFFAOYSA-N 0.000 description 1
- 108010010803 Gelatin Proteins 0.000 description 1
- 208000032843 Hemorrhage Diseases 0.000 description 1
- 102000007625 Hirudins Human genes 0.000 description 1
- 108010007267 Hirudins Proteins 0.000 description 1
- OFOBLEOULBTSOW-UHFFFAOYSA-N Malonic acid Chemical compound OC(=O)CC(O)=O OFOBLEOULBTSOW-UHFFFAOYSA-N 0.000 description 1
- 239000004698 Polyethylene Substances 0.000 description 1
- 239000002202 Polyethylene glycol Substances 0.000 description 1
- 239000004793 Polystyrene Substances 0.000 description 1
- 239000004372 Polyvinyl alcohol Substances 0.000 description 1
- 102000003990 Urokinase-type plasminogen activator Human genes 0.000 description 1
- 108090000435 Urokinase-type plasminogen activator Proteins 0.000 description 1
- 239000002253 acid Substances 0.000 description 1
- 230000001464 adherent effect Effects 0.000 description 1
- 239000001361 adipic acid Substances 0.000 description 1
- 235000011037 adipic acid Nutrition 0.000 description 1
- 125000001931 aliphatic group Chemical group 0.000 description 1
- 230000002965 anti-thrombogenic effect Effects 0.000 description 1
- 229940127218 antiplatelet drug Drugs 0.000 description 1
- 210000000709 aorta Anatomy 0.000 description 1
- 210000000702 aorta abdominal Anatomy 0.000 description 1
- KXNPVXPOPUZYGB-XYVMCAHJSA-N argatroban Chemical compound OC(=O)[C@H]1C[C@H](C)CCN1C(=O)[C@H](CCCN=C(N)N)NS(=O)(=O)C1=CC=CC2=C1NC[C@H](C)C2 KXNPVXPOPUZYGB-XYVMCAHJSA-N 0.000 description 1
- 229960003856 argatroban Drugs 0.000 description 1
- 239000012237 artificial material Substances 0.000 description 1
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- 208000034158 bleeding Diseases 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- RDHPKYGYEGBMSE-UHFFFAOYSA-N bromoethane Chemical compound CCBr RDHPKYGYEGBMSE-UHFFFAOYSA-N 0.000 description 1
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- 238000011156 evaluation Methods 0.000 description 1
- 229950003499 fibrin Drugs 0.000 description 1
- 239000008273 gelatin Substances 0.000 description 1
- 229920000159 gelatin Polymers 0.000 description 1
- 235000019322 gelatine Nutrition 0.000 description 1
- 235000011852 gelatine desserts Nutrition 0.000 description 1
- 238000009998 heat setting Methods 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- ZFGMDIBRIDKWMY-PASTXAENSA-N heparin Chemical compound CC(O)=N[C@@H]1[C@@H](O)[C@H](O)[C@@H](COS(O)(=O)=O)O[C@@H]1O[C@@H]1[C@@H](C(O)=O)O[C@@H](O[C@H]2[C@@H]([C@@H](OS(O)(=O)=O)[C@@H](O[C@@H]3[C@@H](OC(O)[C@H](OS(O)(=O)=O)[C@H]3O)C(O)=O)O[C@@H]2O)CS(O)(=O)=O)[C@H](O)[C@H]1O ZFGMDIBRIDKWMY-PASTXAENSA-N 0.000 description 1
- 229960001008 heparin sodium Drugs 0.000 description 1
- 229940006607 hirudin Drugs 0.000 description 1
- WQPDUTSPKFMPDP-OUMQNGNKSA-N hirudin Chemical compound C([C@@H](C(=O)N[C@@H](CCC(O)=O)C(=O)N[C@@H](CCC(O)=O)C(=O)N[C@@H]([C@@H](C)CC)C(=O)N1[C@@H](CCC1)C(=O)N[C@@H](CCC(O)=O)C(=O)N[C@@H](CCC(O)=O)C(=O)N[C@@H](CC=1C=CC(OS(O)(=O)=O)=CC=1)C(=O)N[C@@H](CC(C)C)C(=O)N[C@@H](CCC(N)=O)C(O)=O)NC(=O)[C@H](CC(O)=O)NC(=O)CNC(=O)[C@H](CC(O)=O)NC(=O)[C@H](CC(N)=O)NC(=O)[C@H](CC=1NC=NC=1)NC(=O)[C@H](CO)NC(=O)[C@H](CCC(N)=O)NC(=O)[C@H]1N(CCC1)C(=O)[C@H](CCCCN)NC(=O)[C@H]1N(CCC1)C(=O)[C@@H](NC(=O)CNC(=O)[C@H](CCC(O)=O)NC(=O)CNC(=O)[C@@H](NC(=O)[C@@H](NC(=O)[C@H]1NC(=O)[C@H](CCC(N)=O)NC(=O)[C@H](CC(N)=O)NC(=O)[C@H](CCCCN)NC(=O)[C@H](CCC(O)=O)NC(=O)CNC(=O)[C@H](CC(O)=O)NC(=O)[C@H](CO)NC(=O)CNC(=O)[C@H](CC(C)C)NC(=O)[C@H]([C@@H](C)CC)NC(=O)[C@@H]2CSSC[C@@H](C(=O)N[C@@H](CCC(O)=O)C(=O)NCC(=O)N[C@@H](CO)C(=O)N[C@@H](CC(N)=O)C(=O)N[C@H](C(=O)N[C@H](C(NCC(=O)N[C@@H](CCC(N)=O)C(=O)NCC(=O)N[C@@H](CC(N)=O)C(=O)N[C@@H](CCCCN)C(=O)N2)=O)CSSC1)C(C)C)NC(=O)[C@H](CC(C)C)NC(=O)[C@H]1NC(=O)[C@H](CC(C)C)NC(=O)[C@H](CC(N)=O)NC(=O)[C@H](CCC(N)=O)NC(=O)CNC(=O)[C@H](CO)NC(=O)[C@H](CCC(O)=O)NC(=O)[C@H]([C@@H](C)O)NC(=O)[C@@H](NC(=O)[C@H](CC(O)=O)NC(=O)[C@@H](NC(=O)[C@H](CC=2C=CC(O)=CC=2)NC(=O)[C@@H](NC(=O)[C@@H](N)C(C)C)C(C)C)[C@@H](C)O)CSSC1)C(C)C)[C@@H](C)O)[C@@H](C)O)C1=CC=CC=C1 WQPDUTSPKFMPDP-OUMQNGNKSA-N 0.000 description 1
- 239000000017 hydrogel Substances 0.000 description 1
- 229920001477 hydrophilic polymer Polymers 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
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- 229940127215 low-molecular weight heparin Drugs 0.000 description 1
- 210000003141 lower extremity Anatomy 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 230000008692 neointimal formation Effects 0.000 description 1
- 230000001575 pathological effect Effects 0.000 description 1
- 229920002647 polyamide Polymers 0.000 description 1
- 229920000573 polyethylene Polymers 0.000 description 1
- 229920001223 polyethylene glycol Polymers 0.000 description 1
- 239000002861 polymer material Substances 0.000 description 1
- 230000000379 polymerizing effect Effects 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 229920002223 polystyrene Polymers 0.000 description 1
- 229920002451 polyvinyl alcohol Polymers 0.000 description 1
- 229920000036 polyvinylpyrrolidone Polymers 0.000 description 1
- 239000001267 polyvinylpyrrolidone Substances 0.000 description 1
- 235000013855 polyvinylpyrrolidone Nutrition 0.000 description 1
- 239000012286 potassium permanganate Substances 0.000 description 1
- 230000008569 process Effects 0.000 description 1
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- 125000001453 quaternary ammonium group Chemical group 0.000 description 1
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- 125000006850 spacer group Chemical group 0.000 description 1
- 230000001954 sterilising effect Effects 0.000 description 1
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- 239000013589 supplement Substances 0.000 description 1
- 229920002994 synthetic fiber Polymers 0.000 description 1
- 229920001059 synthetic polymer Polymers 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- PHWBOXQYWZNQIN-UHFFFAOYSA-N ticlopidine Chemical compound ClC1=CC=CC=C1CN1CC(C=CS2)=C2CC1 PHWBOXQYWZNQIN-UHFFFAOYSA-N 0.000 description 1
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/89—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements comprising two or more adjacent rings flexibly connected by separate members
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/14—Macromolecular materials
- A61L27/18—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
-
- 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
- A61L33/00—Antithrombogenic treatment of surgical articles, e.g. sutures, catheters, prostheses, or of articles for the manipulation or conditioning of blood; Materials for such treatment
- A61L33/06—Use of macromolecular materials
- A61L33/068—Use of macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
-
- D—TEXTILES; PAPER
- D04—BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
- D04B—KNITTING
- D04B21/00—Warp knitting processes for the production of fabrics or articles not dependent on the use of particular machines; Fabrics or articles defined by such processes
- D04B21/02—Pile fabrics or articles having similar surface features
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0076—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof multilayered, e.g. laminated structures
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0015—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in density or specific weight
- A61F2250/0017—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in density or specific weight differing in yarn density
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2509/00—Medical; Hygiene
- D10B2509/06—Vascular grafts; stents
Definitions
- the present invention relates to an artificial blood vessel in which the occurrence of a thrombus-derived occlusion is suppressed when transplanted into a small-diameter blood vessel while maintaining mechanical properties.
- Artificial blood vessels are mainly used to replace pathological biological blood vessels or to form bypasses. Therefore, artificial blood vessels have good biocompatibility with the host, are not toxic, etc., are difficult to deteriorate in the living body, are strong, have little blood leakage, are antithrombogenic, and costly It is required that it is not too high.
- the artificial blood vessel examples include a cloth artificial blood vessel, a polytetrafluoroethylene artificial blood vessel, a biomaterial-derived artificial blood vessel, a synthetic polymer material artificial blood vessel, and a hybrid artificial blood vessel.
- fabrics are mainly used for large-diameter artificial vessels (inner diameter of 10 mm or more) for the aorta, and fabric and PTFE artificial vessels are often used for artificial vessels with medium-diameter (inner diameter 6, 8 mm) for the reconstruction of arteries in the lower limbs.
- fabrics are mainly used for large-diameter artificial vessels (inner diameter of 10 mm or more) for the aorta
- fabric and PTFE artificial vessels are often used for artificial vessels with medium-diameter (inner diameter 6, 8 mm) for the reconstruction of arteries in the lower limbs.
- Patent Document 1 A method for forming a textured structure has been proposed (Patent Document 1).
- Patent Document 1 when the technique of Patent Document 1 is applied to medium- and small-diameter artificial blood vessels, it is still sufficient in terms of functions and characteristics necessary for colonization of endothelial cells when transplanted to medium- and small-diameter blood vessels. There wasn't.
- the present invention retains mechanical properties as an artificial blood vessel, and is less likely to form a thrombus when transplanted into a medium- or small-diameter blood vessel, and has excellent cell fixing properties. It is an object to provide an artificial blood vessel.
- the present invention discloses the following invention.
- At least two types of polyester fibers a multifilament yarn A having a single fiber fineness of 1.0 dtex or more and a total fineness of 33 dtex or less, and a multifilament yarn B having a single fiber fineness of 0.08 dtex or less and a total fineness of 66 dtex or less.
- the inner diameter is 8 mm or less
- the layer thickness is 50 ⁇ m or more and 250 ⁇ m or less
- the multifilament yarn B forms a loop on the inner wall surface of the cylindrical fabric. Artificial blood vessels.
- the artificial blood vessel wherein the number of single fibers of the multifilament B constituting the tubular woven fabric is 40% to 80% of the number of single fibers constituting the tubular woven fabric.
- Any of the above artificial blood vessels further comprising an antithrombotic material.
- the artificial blood vessel of the present invention exhibits the following effects by having the above-described configuration, is not blocked by thrombus formation, can be patted for a long period of time, and has a practical medium-diameter artificial blood vessel. Provided.
- a multifilament yarn A having a single fiber fineness of 1.0 dtex or more and a total fineness of 33 dtex or less
- a multifilament yarn B having a single fiber fineness of 0.08 dtex or less and a total fineness of 66 dtex or less.
- the number of single filaments of the multifilament yarn B of the artificial blood vessel is 40% to 80% of the number of single fibers constituting the tubular woven fabric, further sufficient cell fixing ability, strength retention and water permeability Therefore, it can be used favorably as an artificial blood vessel having a medium or small diameter.
- the artificial blood vessel can be favorably used as an artificial blood vessel having a small diameter.
- the loop of the artificial blood vessel is in a dispersed state or an irregular confounding state, fraying from the anastomosis portion is less likely to occur, so that it can be used favorably as an artificial blood vessel having a medium or small diameter.
- the artificial blood vessel has an accordion structure, the artificial blood vessel has excellent shape stability, so that the artificial blood vessel is prevented from being blocked, bent, or kinked, and can be used favorably as an intermediate blood vessel having a small diameter.
- the artificial blood vessel further contains an antithrombotic material, thrombus generation can be suppressed, and it can be used favorably as a medium or small diameter artificial blood vessel.
- the artificial blood vessel of the present invention is a tubular woven fabric using multifilament yarns of at least two kinds of polyester fibers.
- the artificial blood vessel of the present invention includes a multifilament yarn A having at least a single fiber fineness of 1.0 dtex or more and a total fineness of 33 dtex or less, and a multifilament yarn B having a single fiber fineness of 0.08 dtex or less and a total fineness of 66 dtex or less. Composed.
- the multifilament yarn A a yarn having a single fiber fineness of 1.0 dtex or more and a total fineness of 33 dtex or less is used.
- the fiber of this structure forms the skeleton of an artificial blood vessel, and the surface area that hydrolyzes in the living body that occurs when the artificial blood vessel is left in the body for a long time is reduced, which solves the problem of strength deterioration of the artificial blood vessel. can do.
- the multifilament A has a single fiber fineness of 1.0 dtex or more, preferably 1.0 to 2.2 dtex. The total fineness is 33 dtex or less, preferably 17 to 33 dtex.
- the multifilament yarn B a multifilament yarn having a single fiber fineness of 0.08 dtex or less and a total fineness of 66 dtex or less is used.
- a surface shape having excellent cell fixing properties can be obtained on the inner wall surface. If a multifilament yarn composed of filaments having a single fiber fineness greater than 0.08 dtex is used, the gap between the single fibers is increased, cell fixing properties are reduced, and if a multifilament yarn having a total fineness too large is used, The thickness occupied by the loop increases.
- the single fiber fineness is 0.08 dtex or less, preferably 0.05 to 0.08 dtex, from the viewpoint of cell fixing property and entanglement.
- the total fineness is 66 dtex or less, preferably 44 to 66 dtex.
- a cylindrical woven fabric may be produced using the multifilament A and the multifilament yarn B having the single fiber fineness and the total fineness specified in the present invention.
- a tubular woven fabric is produced using the multifilament A and a multifilament having a single fiber fineness and a total fineness that can be made ultrafine, and the latter multifilament is made ultrafine by chemical or physical means. It is good also as the multifilament B which has the specific single yarn fineness and total fineness.
- the method for producing ultrafine fibers is not particularly limited, but many ultrafine fibers are currently produced by a so-called sea-island structure or a split-type production method.
- an ultrafine fiber is an island part, and a method of dissolving the sea part is used. Another method is to obtain ultrafine fibers by dividing in the length direction.
- a polyamide-based polymer, a polyolefin-based polymer, polystyrene, a soluble polyester-based polymer, or the like is used for the sea portion or the divided portion (for details of the method for producing such ultrafine fibers, see, for example, the document Okamoto M: You can refer to Ultra-fine fiber and its application, Preprints Japan-China Bilated Symposium on Polymer Science and Technology, 256-262, Tokyo, October, 1981. Even if it is a normal fiber thickness, it can be made very fine after formation, minimizing processing problems such as yarn breakage and fluffing when weaving and various yarn processing methods before weaving. Can be suppressed.
- the artificial blood vessel of the present invention uses a polyester fiber as a fiber constituting the multifilament yarn A and the multifilament B.
- the polyester fiber include fibers made of polyethylene terephthalate, polybutylene terephthalate, and the like. It may be a fiber made of a polyester copolymer obtained by copolymerizing polyethylene terephthalate or polybutylene terephthalate with an aliphatic dicarboxylic acid such as isophthalic acid, 5-sodium sulfoisophthalic acid or adipic acid as an acid component.
- the combination of the fibers constituting the multifilament yarns A and B with the aforementioned fibers may be the same or different, and can be combined as appropriate.
- the artificial blood vessel of the present invention is composed of a tubular woven fabric, and the multifilament yarn B forms a loop on the inner wall surface.
- warp the warp yarn of the above-mentioned material and fineness apply it to a loom, and prepare the weft yarn in the same manner.
- a loom for example, a water jet room, an air jet room, a rapier room, a shuttle room, and the like can be used.
- a shuttle room which is excellent in weaving property in a cylindrical shape and a narrow width.
- tubular woven fabric structure composed of the multifilament yarns A and B
- woven fabrics such as plain weave, twill weave, satin weave, and their changed weave and multiple weave are used.
- a weaving structure in which warp yarn (or weft yarn) such as satin weave does not form a crimp with a plurality of weft yarns (or warp yarn), that is, warp yarn (or weft yarn) is a plurality of weft yarns (or warp yarns).
- this portion the portion of the yarn straddling a plurality of yarns
- a pile woven fabric is a typical means. It may be a satin structure, may be a loop formed by bulky processing, or may be a loop based on a yarn length difference expressed by applying heat treatment or chemical treatment. It may be formed by using a high-pressure flow of liquid or gas such as a water jet flow or an air jet flow.
- the loops exist in a dispersed state and / or have an irregular entangled state because excellent anastomosis is provided.
- the presence of a loop in a dispersed state means that the loop does not exist in a concentrated manner in a certain place but exists in a scattered manner, and having an irregular confounding state means that the multifilament has
- the entangled part means a state where a specific arrangement pattern is not regularly repeated but exists irregularly.
- a method using a high-pressure flow using a liquid is efficient, and a method using a water jet flow is preferable from the viewpoint of processing uniformity, safety, and economy.
- the use of the multifilament yarn A and the multifilament B is not limited to either a warp yarn or a weft yarn, and can be used as appropriate.
- the ratio of the number of single fibers of the multifilament yarn B out of the number of single fibers of the tubular woven fabric is 40% or more, and further 50% or more from the viewpoint of cell fixing property and strength maintenance. Preferably there is. Further, this ratio is preferably 80% or more, and more preferably 70% or less, from the viewpoint that sufficient strength retention and water permeability can be easily obtained as a medium-sized or small-diameter artificial blood vessel.
- the ratio of the number of single filaments of the multifilament A and the multifilament B is set to 0.66 or more from the viewpoint of cell fixing property when the number of single filaments in the multifilament A is 1. It is preferably 1 or more.
- the ratio of the multifilament B is preferably 6 or less, more preferably 4 or less, from the viewpoint of strength retention and water permeability.
- a warp yarn beam is produced with each of multifilament A and multifilament B (or fibers that can become the fineness of multifilament B after weaving) with a predetermined single fiber fineness and total fineness. Then, a double beam may be used. Further, in order to obtain a desired ratio of the weft yarn, the weft yarn may be produced with each of the multifilament A and the multifilament B (or fibers that can be made to have a fineness of the multifilament B after weaving).
- Known means can be adopted for the basic weaving method.
- the wall thickness constituting the tubular woven fabric is 50 ⁇ m to 250 ⁇ m, and preferably 100 to 200 ⁇ m from the viewpoint of water permeability and flexibility.
- the wall thickness constituting the tubular woven fabric is 50 ⁇ m to 250 ⁇ m, and preferably 100 to 200 ⁇ m from the viewpoint of water permeability and flexibility.
- the artificial blood vessel of the present invention preferably has a water permeability of 500 ml / min ⁇ cm 2 ⁇ 120 mmHg (16 kPa) or less. This facilitates the entry of endothelial cells and capillaries into the fiber gap, which is preferable from the viewpoint of the formation of endothelial cells. More preferably, it is 400 ml / min ⁇ cm 2 ⁇ 120 mmHg (16 kPa) or less, and 300 to 200 ml / min ⁇ cm 2 ⁇ 120 mmHg (16 kPa) is particularly preferred.
- This water permeability is expressed by the amount of water applied with a pressure corresponding to 120 mmHg (16 kPa) per minute through the fiber gap of a cloth having a width of 1 cm 2 . If the water permeability is too high, endothelial cells and capillaries more easily enter the fiber gap, but blood tends to leak and there is a risk of bleeding.
- the water permeability of the tubular fabric mainly depends on the gap between the multifilament yarns. Therefore, by adjusting the constituent ratio of the multifilament yarn A and the multifilament yarn B or adjusting the weave density, By controlling the space between the filament yarns, a tubular woven fabric having the desired water permeability can be obtained.
- the artificial blood vessel of the present invention has a bellows structure in order to satisfy shape retention and to prevent kinking.
- the bellows structure may be implemented by fitting a cylindrical fabric around a threaded rod whose surface is sufficiently polished, winding an appropriate thread along the thread groove, heat-treating it as it is, and heat setting.
- the bellows may be formed by using a high shrinkage yarn in the horizontal direction and utilizing a difference in shrinkage rate of the yarn.
- the artificial blood vessel of the present invention preferably contains an antithrombotic material.
- antithrombotic material for imparting antithrombogenicity, for example, anticoagulants derived from organisms such as heparin, low molecular weight heparin, urokinase, hirudin may be carried, or synthetic anticoagulants such as argatroban, warfarin, acetylsalicylic acid, ticlopidine and synthetic compounds may be used.
- An antiplatelet drug may be carried.
- a hydrophilic polymer such as polyethylene glycol, polyvinyl alcohol or polyvinyl pyrrolidone may be supported on the multifilament yarn. The method of carrying is not particularly limited.
- medical agent and a polymer is mention
- a method of immobilizing a drug or polymer by a radical reaction using a high energy ray can be mentioned.
- collagen, gelatin, hydrogel or the like is impregnated with a drug or polymer and filled into the gaps of the multifilament yarn.
- Examples of a method for applying an ionic compound such as heparin include a method in which a salt is formed from the ionic compound and a counter ion and the surface of the multifilament yarn is coated. There is also a method in which counter ions are bonded to the surface of the multifilament yarn in advance, and the ionic compound is ion-bonded to the counter ions using ionic interaction. Highly active antithrombogenicity can be imparted, and antithrombogenicity can be stably maintained over a long period of time. Reactive functional groups are chemically introduced into drugs and polymers and immobilized on the fiber surface by chemical reaction. And a method in which counter ions are bonded to the surface in advance and then ion-bonded are preferably used.
- a drug or polymer may be supported on a multifilament yarn used in advance, but it is preferable to impart it after forming a tubular woven fabric from the viewpoint of production cost.
- Fineness According to JIS L 1013 (1999) 8.3.1 A method, the positive fineness was measured at a predetermined load of 0.045 [cN / dtex] to obtain the total fineness.
- Single fiber fineness Calculated by dividing the total fineness by the number of single fibers.
- Thickness of woven fabric In accordance with JIS L 1096: 2010 8.4, 10 thickness layers were used to calm the thickness under a pressure of 23.5 kPa using a thickness measuring machine for five different wall layers of the artificial blood vessel. After waiting for a second, the thickness was measured and the average value was calculated.
- kink resistance was measured by measuring the radius (hereinafter referred to as “kink radius”) in which an artificial blood vessel was looped and apparently bent. As a determination method, a kink radius of 20 mm or less was excellent, 21 to 40 mm was good, 41 to 60 mm was acceptable, and 61 mm or more was unacceptable.
- the produced artificial blood vessel was cut out or cut into an arbitrary square and placed in a petri dish for cell culture.
- Bovine vascular endothelial cells were seeded at a predetermined density on the artificial blood vessel and cultured in an incubator. Three days later, the cell adhesion area ratio was measured with a phase contrast microscope in increments of 1%. As a judgment method, the number of adherent cells was 90% or higher, 70% to 89% was good, 50% to 69% was acceptable, and 49% or less was unacceptable, as compared to a culture using only a petri dish.
- Tables 1 and 2 show the characteristics and performance of the artificial blood vessels of the examples described below.
- the warp yarn and weft yarn are composed of multifilament yarn A having a single fiber fineness of 1.38 dtex and a total fineness of 33 dtex and polyethylene terephthalate copolymerized with 5-sodium sulfoisophthalic acid.
- the multifilament B ′ becomes the multifilament B by the ultrafine processing.
- a warp yarn beam A was produced with a multifilament yarn A and a warp yarn beam B ′ was produced with a multifilament yarn B ′.
- a multifilament yarn A was used to produce a weft shackle A, and a multifilament yarn B ′ was used to produce a weft shattle B ′.
- a multifilament yarn in a tubular woven fabric using a shuttle room which is installed with a double beam of the warp yarn beam A and the warp yarn beam B ′ and also has the weft shuttle A and the multifilament B ′ installed in a double punch.
- Four satin / plain weaving tubular fabrics of warp and plain weave were woven so that the ratio of the number of B single fibers was 60%, and further refined at 98 ° C.
- the obtained woven fabric was treated with an aqueous solution of 4% by weight of sodium hydroxide at 98 ° C.
- an artificial blood vessel composed of a tubular woven fabric having a single filament ratio of the multifilament yarn B of 60%, an inner diameter of 3 mm ⁇ , and a wall thickness of 180 ⁇ m.
- the multifilament yarn B formed loops and these loops existed in a dispersed state. Further, the water permeability was 250 ml / cm 2 / min, the kink resistance was good, the antithrombogenicity, and the cell adhesion were excellent.
- Example 2 An artificial blood vessel made of a tubular woven fabric was produced in the same manner as in Example 1 except that the ratio of the multifilament yarn B was 75%.
- the obtained artificial blood vessel was observed on the inner wall surface with a 100 ⁇ magnification microscope, it was confirmed that the multifilament yarn B formed loops and these loops existed in a dispersed state.
- the water permeability was 310 ml / cm 2 / min, and excellent results were obtained in kink resistance, antithrombogenicity, and cell adhesion.
- Example 3 An artificial blood vessel made of a cylindrical woven fabric was produced by the method described in Example 1 except that the ratio of the number of single filaments of the multifilament yarn B was 30% and the wall thickness was 100 ⁇ m.
- the obtained artificial blood vessel was observed on the inner wall surface with a 100 ⁇ magnification microscope, it was confirmed that the multifilament yarn B formed loops and these loops existed in a dispersed state.
- the water permeability was 190 ml / cm 2 / min, kink resistance had good results, antithrombogenicity was excellent, and cell adhesion had practical results.
- Example 4 An artificial blood vessel made of a tubular woven fabric was prepared by the method described in Example 1 except that the ratio of the number of single filaments of the multifilament yarn B was 90% and the wall thickness was 240 ⁇ m.
- the obtained artificial blood vessel was observed on the inner wall surface with a 100 ⁇ magnification microscope, it was confirmed that the multifilament yarn B formed loops and these loops existed in a dispersed state.
- the water permeability was 470 ml / cm 2 / min, the kink resistance had good results, and the antithrombogenicity and cell adhesiveness had excellent results.
- Example 5 Artificial material made of a cylindrical woven fabric by the method described in Example 1 except that a multifilament yarn A having a single fiber fineness of 2.13 dtex and a total fineness of 17 dtex was used as the warp and weft yarn, and the wall thickness was 50 ⁇ m. Blood vessels were created.
- Example 6 As a warp / weft, an artificial fiber made of a cylindrical woven fabric by the method described in Example 1 except that a multifilament yarn B having a single fiber fineness of 0.05 dtex and a total fineness of 31 dtex was used, and the wall thickness was 150 ⁇ m. Blood vessels were created.
- the obtained artificial blood vessel was observed with a magnifying microscope on the inner wall surface 100 times larger, it was confirmed that the multifilament yarn B formed loops and these loops existed in a dispersed state. Further, the water permeability was 300 ml / cm 2 / min, and kink resistance, antithrombogenicity, and cell adhesion had excellent results.
- Example 7 After weaving the plain weave / plain weave double weft and double weave structure, and inserting a polyethylene film having a width of 4 mm and a thickness of 0.12 mm as a raw spacer into the obtained tubular fabric, the discharge hole diameter was 0.25 mm ⁇ A tubular woven fabric was produced by the method described in Example 1 except that a loop was formed by water jet punching under the conditions of a discharge hole interval of 2.5 mm and a pressure of 70 kg / cm 2 .
- the multifilament yarn B was in a state where the loops were dispersed and irregularly entangled. Further, the water permeability was 140 ml / cm 2 / min, the kink resistance was good, the antithrombogenicity, and the cell adhesion were excellent.
- Example 8 An artificial blood vessel made of a cylindrical woven fabric was produced by the method of Example 1 except that the inner diameter was 7.5 mm ⁇ .
- the inner diameter was 7.5 mm ⁇ .
- the multifilament yarn B formed a loop and existed in a dispersed state.
- the water permeability was 200 ml / cm 2 / min, the kink resistance was good, the antithrombogenicity, and the cell adhesion were excellent.
- Example 9 The cylindrical fabric described in Example 1 was subjected to bellows processing.
- a threaded stainless steel rod was passed through the cylindrical fabric, and a stainless steel wire was wound from the outside of the cylindrical fabric in accordance with the concave portion of the screw.
- the sample was allowed to stand in an oven at 180 ° C. for 30 minutes. After the slow cooling, when the stainless steel wire and the stainless steel rod were removed, a cylindrical bellows structure was formed on the tubular fabric.
- the artificial blood vessel using this tubular fabric had a water permeability of 250 ml / cm 2 / min and had excellent results in kink resistance, antithrombogenicity and cell adhesion.
- Example 10 The tubular fabric described in Example 1 was subjected to antithrombotic processing.
- the antithrombotic treatment was treated with 0.5% aqueous sodium hydroxide and then oxidized with 5% potassium permanganate.
- polyethyleneimine molecular weight 600, Wako Pure Chemical Industries, Ltd.
- a quaternary ammonium reaction of polyethyleneimine immobilized on the fiber surface was performed at 50 ° C. in a 1% methanol solution of ethyl bromide.
- heparin sodium (Wako Pure Chemical Industries) aqueous solution was dipped at 70 ° C. and heparin was ion-bonded to obtain an antithrombotic cylinder used as an artificial blood vessel.
- the obtained artificial blood vessel had better antithrombogenicity than the artificial blood vessel of Example 1, water permeability of 240 ml / cm 2 / min, kink resistance, and excellent cell adhesion. Had characteristics.
- Example 1 An artificial blood vessel made of a tubular woven fabric was prepared by the method described in Example 1 except that the warp yarn / weft yarn was a multifilament yarn A having a single fiber fineness of 1.50 dtex and a total fineness of 84 dtex and a wall thickness of 250 ⁇ m.
- the multifilament yarn B was confirmed to form a loop, but the water permeability was 660 ml / cm 2 / min. It was impossible as a small-diameter artificial blood vessel.
- Example 2 An artificial blood vessel made of a tubular woven fabric was prepared by the method described in Example 1 except that the wall thickness was 310 ⁇ m. When the obtained artificial blood vessel was observed with a 100 ⁇ magnification microscope, the multifilament yarn B was confirmed to form a loop, but the water permeability was 600 ml / cm 2 / min. It was impossible as a small-diameter artificial blood vessel.
- Example 3 An artificial blood vessel made of a tubular woven fabric was prepared by the method described in Example 1 except that the wall thickness was 310 ⁇ m. When the obtained artificial blood vessel was observed with a 100 ⁇ magnification microscope, it was confirmed that the multifilament yarn B formed a loop, but the kink resistance was an artificial blood vessel having a medium or small diameter. It was impossible.
- Example 4 An artificial blood vessel made of a tubular woven fabric was produced by the method described in Example 1 except that the warp yarn / weft yarn was a multifilament yarn B having a single fiber fineness of 0.23 dtex and a total fineness of 33 dtex.
- Example 5 An artificial blood vessel made of a tubular woven fabric was prepared by the method described in Example 1 except that the wall thickness was 30 ⁇ m. When the obtained artificial blood vessel was observed with a 100 ⁇ magnification microscope, the multifilament yarn B was confirmed to form a loop, but the water permeability was 900 ml / cm 2 / min. It was impossible as a small-diameter artificial blood vessel.
- Example 6 An artificial blood vessel made of a tubular woven fabric was prepared by the method described in Example 1 except that the warp yarn / weft yarn was a multifilament yarn B having a single fiber fineness of 0.08 dtex and a total fineness of 84 dtex and a wall thickness of 180 ⁇ m.
- the multifilament yarn B formed a loop when the inner wall surface was observed with a 100 ⁇ magnification microscope. However, the loop protruded excessively on the inner wall surface. Since a thrombus was formed on the inner wall surface, it was impossible as a medium-sized or small-diameter artificial blood vessel.
- Example 7 The tubular fabric of Example 1 was subjected to napping treatment using a raising machine to produce an artificial blood vessel made of the tubular fabric.
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Abstract
Description
(1)単繊維繊度が1.0dtex以上、総繊度が33dtex以下のマルチフィラメント糸Aと、単繊維繊度が0.08dtex以下、総繊度が66dtex以下のマルチフィラメント糸Bの少なくとも2種類のポリエステル繊維で構成してなる、内径が8mm以下、層厚が50μm以上250μm以下の筒状織物であり、かつ、その筒状織物の内壁面にマルチフィラメント糸Bがループを形成していることを特徴とする人工血管。
(2)前記筒状織物を構成する前記マルチフィラメントBの単繊維の本数が筒状織物を構成する単繊維の本数の40%~80%である前記の人工血管。
(3)透水率が500ml/min・cm2・120mmHg(16kPa)以下である前記いずれかの人工血管。
(4)前記マルチフィラメント糸Bが、ループが分散状態で存在するか、または不規則な交絡状態を有する前記いずれかの人工血管。
(5)蛇腹構造の形態を有する前記いずれかの人工血管。
(6)さらに抗血栓性材料を含む前記いずれかの人工血管。
(1)繊度
[総繊度]:JIS L 1013(1999)8.3.1 A法に従って、所定荷重0.045[cN/dtex]で正量繊度を測定して総繊度とした。
[単繊維繊度]:総繊度を単繊維数で除することで算出した。
JIS L 1096:2010 8.4に則り、人工血管の異なる5カ所の壁層について厚さ測定機を用いて、23.5kPaの加圧下、厚さを落ち着かせるために10秒間待った後に厚さを測定し、平均値を算出した。
ISO7198のガイダンスに則り、テーパー度率1/10以下の円錐を垂直にたて、その上にサンプルを被せるように垂直にそっと落とし、止まったサンプルの下端位置の円錐の径を測定した。
ISO7198のガイダンスに則り、人工血管の側壁に、120mmHg(16kPa)の水圧がかかるように水を落下させ、人工血管を通貨して固定冶具から放出された1分間単位面積あたりの漏水量(透水率)を測定した。
ISO7198のガイダンスに則り、耐キンク性は人工血管をループさせていき、外見上明らかに折れ曲がりが生じる半径(以下「キンク半径」という。)を測定した。判定方法として、キンク半径が20mm以下を優、21~40mmを良、41~60mmを可、61mm以上を不可とした。
ラットの腹部大動脈を約3cm剥離し、その両端をクランプにて縛り、血流を遮断させた後、動脈の中央部を切断し、その間を人工血管の両方の末端で接合した後、クランプを除去し、血流を再開させ、1週間後に摘出し、内壁面を観察する。判定方法として、開存したものを優、血栓で閉塞したものを不可とした。
作製した人工血管を任意の四角形に切り抜き、または切り開き、細胞培養用シャーレに置いた。該人工血管上にウシ血管内皮細胞を所定の密度で播種し、インキュベーター内にて培養した。3日後の細胞を位相差顕微鏡にて細胞の接着面積の比率を1%刻みで測定した。判定方法として、シャーレのみで培養したものと比較して、接着細胞数が、90%以上を優良、70%~89%を良好、50%~69%を可、49%以下を不可とした。
タテ糸及びヨコ糸(裏糸)にポリエステル繊維の単繊維繊度が1.38dtex、総繊度33dtexのマルチフィラメント糸Aと海成分ポリマーが5-ナトリウムスルホイソフタル酸を共重合したポリエチレンテレフタレートで構成され、島成分ポリマーがポリエチレンテレフタレートで構成される海島繊維(海/島(質量比)=20/80の比率にて、島成分の数70)で単繊維繊度が7.3dtex、総繊度66dtexで無撚りのマルチフィラメント糸B’を使用した。このマルチフィラメントB’は極細化処理によりマルチフィラメントBとなる。上記タテ糸を用い、マルチフィラメント糸AおよびマルチフィラメントB’それぞれについて、ビーマーにてマルチフィラメント糸Aでタテ糸ビームA、マルチフィラメント糸B’でタテ糸ビームB’をそれぞれ作製した。上記ヨコ糸を用い、マルチフィラメント糸AおよびマルチフィラメントB’それぞれについて、管巻機にてマルチフィラメント糸Aでヨコ糸シャットルA、マルチフィラメント糸B’でヨコ糸シャットルB’をそれぞれ作製した。上記タテ糸ビームA、タテ糸ビームB’の2重ビームにて設置し、また上記ヨコ糸シャットルAおよびマルチフィラメントB’を2丁打ちで設置したシャットルルームを用い、筒状織物におけるマルチフィラメント糸Bの単繊維の本数の比率が60%になるように4枚朱子/平織りの経2重緯2重組織の筒状織物を織り、さらに98℃で精練した。得られた織物を98℃の水酸化ナトリウム4質量%水溶液で20分間処理して前述の海島複合繊維の海成分を完全に溶脱させ、マルチフィラメントBの単繊維繊度を0.08dtex、総繊度53dtexに極細化した。次いで乾熱120℃で乾燥した後、滅菌し、マルチフィラメント糸Bの単繊維の比率が60%、内径3mmφ、壁厚180μmの筒状織物からなる人工血管を得た。
マルチフィラメント糸Bの割合を75%にした以外は実施例1と同じ方法で筒状織物からなる人工血管を作製した。得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成し、それらのループは分散状態で存在していることが確認された。また、透水率310ml/cm2/minであり、耐キンク性、および、抗血栓性、および、細胞接着性は優良な結果を得た。
マルチフィラメント糸Bの単繊維の本数の割合を30%にしたことと、壁厚を100μmとしたこと以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成し、それらのループは分散状態で存在していることが確認された。透水率190ml/cm2/minであり、耐キンク性は良好な結果を有し、抗血栓性は優良、細胞接着性は、実用可能な結果を有していた。
マルチフィラメント糸Bの単繊維の本数の割合を90%にしたことと、壁厚を240μmとしたこと以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成し、それらのループは分散状態で存在していることが確認された。透水率470ml/cm2/minであり、耐キンク性は良好な結果を有し、抗血栓性および、細胞接着性は優良な結果を有していた。
タテ糸・ヨコ糸として、単繊維繊度が2.13dtex、総繊度17dtexのマルチフィラメント糸Aを使用したことと、壁厚が50μmとした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。
[実施例6]
タテ糸・ヨコ糸として、単繊維繊度が0.05dtex、総繊度31dtexのマルチフィラメント糸Bを使用したことと、壁厚が150μmとした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。
織組織を平織り/平織りの経2重緯2重組織としたことと、得られた筒状織物に、素スペーサーとして幅4mm、厚み0.12mmのポリエチレンフィルムを挿入した後、吐出孔径0.25mmφ、吐出孔間隔2.5mm、圧力70kg/cm2の条件でウォータージェットパンチ処理をしてループを形成させたこと以外は実施例1記載の方法で筒状織物を作製した。
内径を7.5mmφとしたこと以外は実施例1の方法で筒状織物からなる人工血管を作製した。得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成し、分散状態で存在していることが確認された。透水率200ml/cm2/minであり、耐キンク性は良好、抗血栓性および、細胞接着性は優良な結果を有していた。
実施例1に記載の筒状織物に蛇腹加工を行った。蛇腹加工は、ねじを切ったステンレス棒を筒状織物に通し、ねじの凹部に合わせてステンレス線を筒状織物の外から巻き付けた。その状態で、その試料を180℃のオーブンの中で30分静置した。徐冷後、ステンレスワイヤー線とステンレス棒を取り外したところ、筒状織物には円筒蛇腹構造が形成されていた。
実施例1に記載の筒状織物に抗血栓加工を行った。抗血栓加工は、0.5%水酸化ナトリウム水溶液で処理した後、次いで5%過マンガン酸カリウムで酸化処理した。つづいて、0.1% 1-(3-ジメチルアミノプロピル)-3-エチルカルボジイミドの存在下で、ポリエチレンイミン(分子量600、和光純薬工業社)を加えて筒状物の繊維とポリエチレンイミンを反応させた。更に、臭化エチルの1%メタノール溶液中、50℃で繊維表面に固定化されたポリエチレンイミンの第4級アンモニウム化反応を行った。最後に、0.8%ヘパリンナトリウム(和光純薬工業)水溶液を70℃にて浸漬処理してヘパリンをイオン結合させたものを、人工血管として用いる抗血栓筒状物とした。得られた人工血管は、実施例1の人工血管に比べて、より良好な抗血栓性を備えており、透水率240ml/cm2/min、耐キンク性を備え、細胞接着性においても優れた特性を有していた。
タテ糸・ヨコ糸として、単繊維繊度が1.50dtex、総繊度84dtexのマルチフィラメント糸Aと壁厚を250μmにした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。
壁厚を310μmにした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成していることが確認されたが、透水率が600ml/cm2/minであり、中、小口径の人工血管として不可であった。
壁厚を310μmにした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成していることが確認されたが、耐キンク性が、中、小口径の人工血管として不可であった。
タテ糸・ヨコ糸として、単繊維繊度が0.23dtex、総繊度33dtexのマルチフィラメント糸Bとした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。
壁厚を30μmにした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。 得られた人工血管は、内壁面を100倍の拡大顕微鏡で観察すると、マルチフィラメント糸Bがループを形成していることが確認されたが、透水率が900ml/cm2/minであり、中、小口径の人工血管として不可であった。
タテ糸・ヨコ糸として、単繊維繊度が0.08dtex、総繊度84dtexのマルチフィラメント糸Bと壁厚を180μmにした以外は実施例1記載の方法で筒状織物からなる人工血管を作製した。
実施例1の筒状織物に対して、起毛機を用いた立毛処理を行って筒状織物からなる人工血管を作製した。
Claims (6)
- 単繊維繊度が1.0dtex以上、総繊度が33dtex以下のマルチフィラメント糸Aと、単繊維繊度が0.08dtex以下、総繊度が66dtex以下のマルチフィラメント糸Bの少なくとも2種類のポリエステル繊維で構成され、内径が8mm以下、層厚が50μm以上250μm以下の筒状織物であり、かつ、その筒状織物の内壁面にマルチフィラメント糸Bがループを形成していることを特徴とする人工血管。
- 前記筒状織物を構成する前記マルチフィラメントBの単繊維の本数が筒状織物を構成する単繊維の本数の40%~80%である請求項1に記載の人工血管。
- 透水率が500ml/min・cm2・120mmHg(16kPa)以下である請求項1又は2に記載の人工血管。
- 前記のマルチフィラメント糸Bが、複数のループ状の形態をとり、これらのループが分散状態で存在するか、または、不規則な交絡状態を有する請求項1~3いずれかに記載の人工血管。
- 蛇腹構造の形態を有する請求項1~4いずれかに記載の人工血管。
- さらに抗血栓性材料を含む請求項1~5いずれかに記載の人工血管。
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ES14788777.2T ES2649170T3 (es) | 2013-04-26 | 2014-04-23 | Vaso sanguíneo artificial |
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EP3085335A4 (en) * | 2013-12-18 | 2017-07-19 | Toray Industries, Inc. | Artificial blood vessel |
CN115192768A (zh) * | 2022-06-14 | 2022-10-18 | 山东大学齐鲁医院 | 一种复合材料人工血管及其制造工艺 |
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CN114959989B (zh) * | 2022-06-29 | 2023-11-28 | 山东黄河三角洲纺织科技研究院有限公司 | 一种人造血管及其立体编织方法 |
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RU2653835C2 (ru) | 2018-05-14 |
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US9943424B2 (en) | 2018-04-17 |
EP2990010A1 (en) | 2016-03-02 |
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