WO2023140422A1 - 히알루론산을 함유하는 흡수성 봉합사 및 이의 제조방법 - Google Patents
히알루론산을 함유하는 흡수성 봉합사 및 이의 제조방법 Download PDFInfo
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- WO2023140422A1 WO2023140422A1 PCT/KR2022/003958 KR2022003958W WO2023140422A1 WO 2023140422 A1 WO2023140422 A1 WO 2023140422A1 KR 2022003958 W KR2022003958 W KR 2022003958W WO 2023140422 A1 WO2023140422 A1 WO 2023140422A1
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- WO
- WIPO (PCT)
- Prior art keywords
- poly
- weight
- hyaluronic acid
- absorbable suture
- acid
- Prior art date
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- KIUKXJAPPMFGSW-DNGZLQJQSA-N (2S,3S,4S,5R,6R)-6-[(2S,3R,4R,5S,6R)-3-Acetamido-2-[(2S,3S,4R,5R,6R)-6-[(2R,3R,4R,5S,6R)-3-acetamido-2,5-dihydroxy-6-(hydroxymethyl)oxan-4-yl]oxy-2-carboxy-4,5-dihydroxyoxan-3-yl]oxy-5-hydroxy-6-(hydroxymethyl)oxan-4-yl]oxy-3,4,5-trihydroxyoxane-2-carboxylic acid Chemical compound CC(=O)N[C@H]1[C@H](O)O[C@H](CO)[C@@H](O)[C@@H]1O[C@H]1[C@H](O)[C@@H](O)[C@H](O[C@H]2[C@@H]([C@@H](O[C@H]3[C@@H]([C@@H](O)[C@H](O)[C@H](O3)C(O)=O)O)[C@H](O)[C@@H](CO)O2)NC(C)=O)[C@@H](C(O)=O)O1 KIUKXJAPPMFGSW-DNGZLQJQSA-N 0.000 title claims abstract description 118
- 229920002674 hyaluronan Polymers 0.000 title claims abstract description 118
- 229960003160 hyaluronic acid Drugs 0.000 title claims abstract description 118
- 238000004519 manufacturing process Methods 0.000 title claims abstract description 17
- 229920000642 polymer Polymers 0.000 claims abstract description 44
- JVTAAEKCZFNVCJ-REOHCLBHSA-N L-lactic acid Chemical compound C[C@H](O)C(O)=O JVTAAEKCZFNVCJ-REOHCLBHSA-N 0.000 claims abstract description 30
- VPVXHAANQNHFSF-UHFFFAOYSA-N 1,4-dioxan-2-one Chemical compound O=C1COCCO1 VPVXHAANQNHFSF-UHFFFAOYSA-N 0.000 claims abstract description 29
- AEMRFAOFKBGASW-UHFFFAOYSA-N Glycolic acid Chemical compound OCC(O)=O AEMRFAOFKBGASW-UHFFFAOYSA-N 0.000 claims abstract description 22
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 claims abstract description 21
- 235000014655 lactic acid Nutrition 0.000 claims abstract description 11
- 239000004310 lactic acid Substances 0.000 claims abstract description 11
- 239000000463 material Substances 0.000 claims abstract description 7
- 229920002463 poly(p-dioxanone) polymer Polymers 0.000 claims description 47
- 239000000622 polydioxanone Substances 0.000 claims description 47
- 230000002745 absorbent Effects 0.000 claims description 39
- 239000002250 absorbent Substances 0.000 claims description 39
- 239000002245 particle Substances 0.000 claims description 22
- 229920001432 poly(L-lactide) Polymers 0.000 claims description 21
- 229920001577 copolymer Polymers 0.000 claims description 20
- 238000009987 spinning Methods 0.000 claims description 19
- 230000014759 maintenance of location Effects 0.000 claims description 18
- 229920000954 Polyglycolide Polymers 0.000 claims description 16
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 16
- 238000002156 mixing Methods 0.000 claims description 15
- 229920001610 polycaprolactone Polymers 0.000 claims description 14
- 229920000747 poly(lactic acid) Polymers 0.000 claims description 11
- 239000002994 raw material Substances 0.000 claims description 10
- 238000002844 melting Methods 0.000 claims description 9
- 230000008018 melting Effects 0.000 claims description 9
- LBJBPGRQRGLKPL-UHFFFAOYSA-N 7-(4-chlorophenyl)-5-naphthalen-2-yl-6-sulfanylidene-2,3-dihydro-1h-pyrrolo[3,4-e][1,4]diazepin-8-one Chemical compound C1=CC(Cl)=CC=C1N1C(=S)C(C(=NCCN2)C=3C=C4C=CC=CC4=CC=3)=C2C1=O LBJBPGRQRGLKPL-UHFFFAOYSA-N 0.000 claims description 7
- 101000691618 Homo sapiens Inactive phospholipase C-like protein 1 Proteins 0.000 claims description 7
- 101000604957 Homo sapiens Phosducin-like protein Proteins 0.000 claims description 7
- 102100026207 Inactive phospholipase C-like protein 1 Human genes 0.000 claims description 7
- 102100038218 Phosducin-like protein Human genes 0.000 claims description 7
- 229920000848 poly(L-lactide-ε-caprolactone) Polymers 0.000 claims description 7
- 239000004632 polycaprolactone Substances 0.000 claims description 7
- 238000002054 transplantation Methods 0.000 claims description 5
- 239000000843 powder Substances 0.000 claims 1
- 230000007423 decrease Effects 0.000 description 15
- 239000000155 melt Substances 0.000 description 12
- 239000000523 sample Substances 0.000 description 11
- 238000000034 method Methods 0.000 description 9
- 239000004633 polyglycolic acid Substances 0.000 description 9
- 239000004626 polylactic acid Substances 0.000 description 9
- 238000012360 testing method Methods 0.000 description 7
- 206010052428 Wound Diseases 0.000 description 6
- 208000027418 Wounds and injury Diseases 0.000 description 6
- 238000002835 absorbance Methods 0.000 description 5
- 238000002513 implantation Methods 0.000 description 5
- 230000003020 moisturizing effect Effects 0.000 description 5
- 239000000243 solution Substances 0.000 description 5
- 238000000354 decomposition reaction Methods 0.000 description 4
- 238000001356 surgical procedure Methods 0.000 description 4
- PAPBSGBWRJIAAV-UHFFFAOYSA-N ε-Caprolactone Chemical compound O=C1CCCCCO1 PAPBSGBWRJIAAV-UHFFFAOYSA-N 0.000 description 4
- 241000894006 Bacteria Species 0.000 description 2
- 241001465754 Metazoa Species 0.000 description 2
- 239000002253 acid Substances 0.000 description 2
- 230000009471 action Effects 0.000 description 2
- 239000007853 buffer solution Substances 0.000 description 2
- 210000004027 cell Anatomy 0.000 description 2
- 230000008859 change Effects 0.000 description 2
- 230000006866 deterioration Effects 0.000 description 2
- 239000012153 distilled water Substances 0.000 description 2
- 238000002474 experimental method Methods 0.000 description 2
- 238000000338 in vitro Methods 0.000 description 2
- 208000015181 infectious disease Diseases 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 238000000691 measurement method Methods 0.000 description 2
- 230000000149 penetrating effect Effects 0.000 description 2
- 239000002953 phosphate buffered saline Substances 0.000 description 2
- 230000000704 physical effect Effects 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 239000010453 quartz Substances 0.000 description 2
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N silicon dioxide Inorganic materials O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 description 2
- 239000012086 standard solution Substances 0.000 description 2
- 230000029663 wound healing Effects 0.000 description 2
- 102100032912 CD44 antigen Human genes 0.000 description 1
- 101000868273 Homo sapiens CD44 antigen Proteins 0.000 description 1
- 241000361919 Metaphire sieboldi Species 0.000 description 1
- 230000001580 bacterial effect Effects 0.000 description 1
- 229920006167 biodegradable resin Polymers 0.000 description 1
- 230000001851 biosynthetic effect Effects 0.000 description 1
- 229920001400 block copolymer Polymers 0.000 description 1
- 239000000872 buffer Substances 0.000 description 1
- 238000011109 contamination Methods 0.000 description 1
- 230000008602 contraction Effects 0.000 description 1
- 239000013068 control sample Substances 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- LOKCTEFSRHRXRJ-UHFFFAOYSA-I dipotassium trisodium dihydrogen phosphate hydrogen phosphate dichloride Chemical compound P(=O)(O)(O)[O-].[K+].P(=O)(O)([O-])[O-].[Na+].[Na+].[Cl-].[K+].[Cl-].[Na+] LOKCTEFSRHRXRJ-UHFFFAOYSA-I 0.000 description 1
- 210000002919 epithelial cell Anatomy 0.000 description 1
- 230000012010 growth Effects 0.000 description 1
- 125000002887 hydroxy group Chemical group [H]O* 0.000 description 1
- 238000007654 immersion Methods 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000005445 natural material Substances 0.000 description 1
- 238000003825 pressing Methods 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 230000017423 tissue regeneration Effects 0.000 description 1
- 238000010792 warming Methods 0.000 description 1
- 230000037303 wrinkles Effects 0.000 description 1
Classifications
-
- 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
- A61L17/10—At least partially resorbable materials containing macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/06—Needles ; Sutures; Needle-suture combinations; Holders or packages for needles or suture materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
-
- 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
- A61L17/10—At least partially resorbable materials containing macromolecular materials
- A61L17/12—Homopolymers or copolymers of glycolic acid or lactic acid
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L5/00—Compositions of polysaccharides or of their derivatives not provided for in groups C08L1/00 or C08L3/00
- C08L5/08—Chitin; Chondroitin sulfate; Hyaluronic acid; Derivatives thereof
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L67/00—Compositions of polyesters obtained by reactions forming a carboxylic ester link in the main chain; Compositions of derivatives of such polymers
- C08L67/02—Polyesters derived from dicarboxylic acids and dihydroxy compounds
- C08L67/025—Polyesters derived from dicarboxylic acids and dihydroxy compounds containing polyether sequences
Definitions
- the present invention relates to an absorbable suture containing hyaluronic acid in an absorbable polymer and a manufacturing method thereof.
- a suture is used as a thread for suturing a body part damaged by surgery or the like, and a human body part is sutured with the suture by connecting an injection needle to an end of the suture and penetrating a part of the body through the suture.
- Sutures are divided into non-absorbable sutures, which are removed after a certain period of time has elapsed after surgery, and absorbable sutures that are biodegraded and disappear after a certain period of time in the human body.
- Absorbable sutures do not require a separate procedure for removal, and are naturally decomposed and disappear. Due to their convenience, absorbable sutures have recently been widely used, and their market share is increasing worldwide.
- Sutures are divided into a monofilament structure of a single structure and a multifilament structure of a complex structure. In the case of a multifilament suture, flexibility is secured. On the other hand, sutures need to maintain knot strength and elongation above a certain level in order to firmly seal and maintain damaged parts of the human body. Absorbable sutures using absorbable polymers may have lower strength than non-absorbable sutures due to their natural decomposition after a certain period of time.
- an object to be solved by the present invention is to provide an absorbable suture capable of imparting a moisturizing effect to the skin in addition to being decomposed in the body, and a manufacturing method thereof.
- an object of the present invention is to provide an absorbable suture capable of releasing hyaluronic acid continuously and in an appropriate amount even after a long time has elapsed after suture treatment by including hyaluronic acid on the inside as well as on the surface of the absorbable suture, and a manufacturing method thereof.
- an object of the present invention is to provide an absorbable suture capable of preventing deterioration in knot strength, elongation, etc., which are physical properties required of an absorbable suture, and a manufacturing method thereof, while including hyaluronic acid in the absorbable suture.
- Absorbable suture according to an embodiment of the present invention for solving the above problems is poly L-lactic acid (PLLA, Poly[L-Lactic Acid]), polylactic acid (PLA, Poly[Lactic Acid]), polydioxanone (PDO, Poly[p-dioxanone]), polycaprolactone (PCL, Poly[ ⁇ -carprolactone]), polyglycolic acid (PGA, Poly[glycolic acid]), polyglycolic acid caprolactone (PGCL) , Poly[glycolic Acid-co- ⁇ -carprolactone), Poly[L-lactic-co-glycolic Acid (PLGA), Poly L-lactic acid caprolactone copolymer (PLCL, Poly[L-lactide-co- ⁇ -caprolactone]), Polydioxanone caprolactone copolymer (PDCL, Poly[p-dioxanone-co- ⁇ -caprolactone]), and polydioxanone L-lactic acid copolymer
- the absorbable suture may be composed of a monofilament, and the hyaluronic acid may be distributed inside and on the surface of the monofilament.
- the hyaluronic acid is included in the range of 0.5% by weight or more to less than 5.0% by weight of the total weight of the absorbable suture.
- the hyaluronic acid is included in the range of 0.5% by weight or more and 4.0% by weight or less based on the total weight of the absorbable suture.
- the hyaluronic acid is included in the range of 0.5% by weight or more and 3.0% by weight or less based on the total weight of the absorbable suture.
- the absorbable suture may have a breaking strength retention (BSR) of 40% or more to 80% or less 2 weeks after transplantation.
- BSR breaking strength retention
- the water absorbent polymer is composed of polydioxanone (PDO, Poly[p-dioxanone]), and the melt index (Ml) of the polydioxanone (PDO, Poly[p-dioxanone]) is 2 g / 10 min or more. It can be characterized in that the range of 16 g / 10 min or less.
- a method for manufacturing an absorbable suture according to an embodiment of the present invention to solve the above problems is poly L-lactic acid (PLLA, Poly[L-Lactic Acid]), poly(PLA, Poly[Lactic Acid]), polydioxanone (PDO, Poly[p-dioxanone]), polycaprolactone (PCL, Poly[ ⁇ -carprolactone]), polyglycolic acid (PGA, Poly[glycolic acid]), polyglycolic acid capro Lactone (PGCL, Poly[glycolic Acid-co- ⁇ -carprolactone), Poly[L-lactic-co-glycolic Acid (PLGA, Poly[L-lactic-co-glycolic Acid), Poly L-lactic acid caprolactone copolymer (PLCL, Poly[L-lactide-co- ⁇ -caprolactone]), polydioxanone caprolactone copolymer (PDCL, Poly[p-dioxanone-co- ⁇ -caprolactone]),
- the average particle size of the hyaluronic acid may be characterized in that the range of 1 ⁇ m to 400 ⁇ m.
- the average particle size of the hyaluronic acid is in the range of 1 ⁇ m to 300 ⁇ m, and the absorbable suture may contain the hyaluronic acid in an amount of 0.5% by weight or more and 4.0% by weight or less based on the total weight of the absorbable suture.
- the average particle size of the hyaluronic acid is in the range of 1 ⁇ m to 300 ⁇ m, and the hyaluronic acid may be included in the range of 0.5% by weight or more and 3.0% by weight or less based on the total weight of the absorbable suture.
- the water absorbent polymer is composed of polydioxanone (PDO, Poly[p-dioxanone]), and the melt index (Ml) of the polydioxanone (PDO, Poly[p-dioxanone]) is 2 g / 10 min or more. It can be characterized in that the range of 16 g / 10 min or less.
- the mixing step when the water absorbent polymer is completely dissolved, the hyaluronic acid is added and mixed. It may be characterized by spinning in a state in which the temperature ranges from 200° C. to 200° C. and the pressure ranges from 20 bar to 60 bar.
- the stretching step may include a first stretching step of stretching at a stretching ratio of 1:3 to 1:7 and a second stretching step for stretching at a stretching ratio of 1:1.1 to 1:2, and may further include a step of contracting at a ratio of 1:0.5 to 1:0.9 after the stretching step.
- the absorbable suture can perform a function of imparting a moisturizing effect to the skin in addition to being decomposed in the body after the procedure.
- hyaluronic acid may be included not only on the surface of the absorbable suture but also on the inside of the suture so that hyaluronic acid can be released continuously and in an appropriate amount even after a long time has elapsed after the suture procedure.
- An absorbable suture according to an embodiment of the present invention is poly L-lactic acid (PLLA, Poly[L-Lactic Acid]), polylactic acid (PLA, Poly[Lactic Acid]), polydioxanone (PDO, Poly[p-dioxanone]), polycaprolactone (PCL, Poly[ ⁇ -carprolactone]), polyglycolic acid (PGA, Poly[glycolic acid]), polyglycolic acid caprolactone (PGCL, poly[glycolic acid]).
- PLLA Poly[L-Lactic Acid]
- PLA Poly[Lactic Acid]
- PDO Poly[p-dioxanone]
- PCL Polycaprolactone
- PCL Poly[ ⁇ -carprolactone]
- PGA Poly[glycolic acid]
- polyglycolic acid caprolactone poly[glycolic acid]
- the absorbable suture of the present invention can be implanted into the body to maintain physical tension for a certain period of time and maintain a sutured state at the suture site. Or it can be used for pulling the skin and removing wrinkles.
- Absorbable sutures undergo a decomposition period of 3 to 24 months without limitation after surgery or procedure, and are self-degrading in the body, so there is no need for a separate medical action to remove the suture, and the decomposition period can be adjusted by changing the type or content of the absorbable polymer.
- Hyaluronic acid is a biosynthetic natural substance that is abundantly present in the skin of animals, etc., is a hydrophilic substance with a lot of hydroxyl groups (-OH), and plays a role in moisturizing the skin of people or animals. It is also present in human skin, and is known to be particularly abundant in earthworm skin, and in addition to moisturizing action, it can react with CD44 protein expressed in various epithelial cells to regulate various physiological actions.
- the absorbent polymer of the present invention is poly L-lactic acid (PLLA, Poly[L-Lactic Acid]), polylactic acid (PLA, Poly[Lactic Acid]), polydioxanone (PDO, Poly[p-dioxanone]), polycaprolactone (PCL, Poly[ ⁇ -carprolactone]), polyglycolic acid (PGA, Poly[glycolic acid]), polyglycolic acid-co- ⁇ -car prolactone), polylactic-coglycolic acid (PLGA, Poly[L-lactic-co-glycolic Acid), poly L-lactic acid caprolactone copolymer (PLCL, Poly[L-lactide-co- ⁇ -caprolactone]), polydioxanone caprolactone copolymer (PDCL, Poly[p-dioxanone-co- ⁇ -caprolactone]), and polydioxanone L-lactic acid copolymer (PLDA, Poly[L-lactic acid-co -p-
- the absorbable suture of the present invention may be composed of monofilaments, and the hyaluronic acid may be distributed inside and on the surface of the monofilaments. Since the absorbable suture is composed of a monofilament, it is possible to prevent contamination due to bacterial growth. More specifically, when the absorbable suture is composed of multifilaments, bacteria can penetrate between several strands, increasing the probability of infection. In the present invention, since the suture is composed of monofilaments, it is possible to minimize the occurrence of infection by bacteria penetrating between the sutures.
- hyaluronic acid By evenly including hyaluronic acid not only on the surface of the monofilament but also inside the monofilament, it is possible to continuously release hyaluronic acid into the skin over time even though the hyaluronic acid is released immediately after the suture sutures the skin.
- the absorbable suture of the present invention can continuously release hyaluronic acid until decomposition is completed after the skin is sutured by evenly distributing hyaluronic acid inside and outside the suture. If hyaluronic acid is simply distributed (coated) only on the surface of the suture, a problem may arise in that all hyaluronic acid is released in a short time after skin tissue is sutured, and if hyaluronic acid is separately contained only in the core of the suture, a problem in that hyaluronic acid is released only after a long time has passed since the suture is implanted into the skin may occur.
- hyaluronic acid is distributed inside and outside the suture, so that the hyaluronic acid is released immediately after the implantation of the absorbable suture, while the absorbable suture is decomposed, so that the hyaluronic acid can be continuously released into the skin, so that the skin moisturizing effect can be continuously provided.
- the absorbable suture is characterized in that the hyaluronic acid is included in the range of more than 0.1% by weight and less than 5.0% by weight of the total weight, for example, in the range of more than 0.1% by weight and less than 4.0% by weight, in the range of more than 0.1% by weight and less than 3.0% by weight, in the range of more than 0.5% by weight and less than 5.0% by weight, in the range of more than 0.5% by weight and less than 4.0% by weight, 0 .5% by weight or more to 3.0% by weight or less, 1.0% by weight or more to less than 5.0% by weight, 1.0% by weight or more to 4.0% by weight or less, or 1.0% by weight or more to 3.0% by weight or less.
- the knot strength of the absorbable suture is in the range of 40 N or more to 60 N or less, and the knot elongation is 20% or more to 40% or less.
- European standards for absorbable sutures stipulate that the knot strength should be 39 N or more, and if the knot strength falls below 40 N, it may be difficult to use the suture as a suture.
- the knot strength may be, for example, in the range of 40 N or more to 60 N or less when the diameter of the absorbable suture is in the range of 0.4 mm or more to 0.5 mm or less.
- the diameter of the absorbable suture may be in the range of 0.1 mm or more to 0.2 mm or less, 0.2 mm or more to 0.3 mm or less, 0.3 mm or more to 0.4 mm or less, or 0.4 mm or more to 0.5 mm or less, and can be adjusted according to the diameter desired by the user.
- knot elongation refers to the ratio (%) of the initial length to the length extended to the maximum load, and when the knot elongation is 0%, it may be practically difficult to use it as a suture.
- the absorbable suture maintains an appropriate tension, so that it may be convenient to use in surgery or procedures such as skin suture.
- the absorbable suture may have a breaking strength retention (BSR) of 40% or more to 80% or less 2 weeks after transplantation.
- Breaking Strength Retention is to confirm the strength retention in the body through an in-vitro test, and to confirm the retention strength compared to the initial strength.
- the strength gradually decreases as the wound heals, and the change in strength over time must be measured.
- the period required for wound healing is about 2 weeks, and the strength of the suture must be maintained within this period.
- the Breaking Strength Retention (BSR) is less than 30% 2 weeks after transplantation, the strength of the suture decreases before the wound heals, making it difficult to perform its function as a suture.
- it should be 40% or more.
- the absorbent polymer is composed of polydioxanone (PDO, Poly[p-dioxanone]), and the melt index (Ml) of the polydioxanone (PDO, Poly[p-dioxanone]) is 2 g / 10 min or more. It can be characterized in that the range of 16 g / 10 min or less. In the above melt index (MI) range, it is possible to prevent a rapid decrease in Breaking Strength Retention (BSR) after 2 weeks after implantation and to enable use as an absorbable suture.
- MI melt index
- BSR Breaking Strength Retention
- the present invention provides a manufacturing method for manufacturing the absorbable suture.
- the method for manufacturing the absorbable suture will be described, and descriptions of overlapping contents with those described in the absorbable suture will be omitted.
- An absorbable suture manufacturing method includes poly L-lactic acid (PLLA, Poly[L-Lactic Acid]), polylactic acid (PLA, Poly[Lactic Acid]), polydioxanone (PDO, Poly[p-dioxanone]), polycaprolactone (PCL, Poly[ ⁇ -carprolactone]), polyglycolic acid (PGA, Poly[glycolic acid]), polyglycolic acid caprolactone (PGCL, Poly[ glycolic Acid-co- ⁇ -carprolactone), Poly[L-lactic-co-glycolic Acid (PLGA), Poly L-lactic acid caprolactone copolymer (PLCL, Poly[L-lactide-co- ⁇ -caprolactone]), Poly[p-dioxanone-co- ⁇ -caprolactone] (PDCL, Poly[p-dioxanone-co- ⁇ -caprolactone]), and polydioxanone L-lactic acid copolymer (PLDA), Poly[glycolix
- an absorbent polymer raw material containing at least one material selected from the group consisting of poly[L-lactic acid-co-p-dioxanone] and a raw material of powdered hyaluronic acid, mixing the absorbent polymer and the hyaluronic acid, spinning the absorbent polymer and the hyaluronic acid, and stretching the spun suture, wherein the hyaluronic acid in the absorbent suture has a total weight of 0 It is characterized in that it is included in the range of more than .1% by weight and less than 5.0% by weight.
- the hyaluronic acid is characterized in that it is included in the range of more than 0.1% by weight to less than 5.0% by weight, for example, more than 0.1% by weight to less than 4.0% by weight, more than 0.1% by weight to less than 3.0% by weight, more than 0.5% by weight to less than 5.0% by weight, more than 0.5% to less than 4.0% by weight, more than 0.5% to 3.0% by weight It may be characterized in that it includes in the range of less than or equal to wt%, in the range of 1.0 wt% or more to less than 5.0 wt%, in the range of 1.0 wt% or more to 4.0 wt% or less, or in the range of 1.0 wt% or more to 3.0 wt% or less. Within the above range, it is possible to minimize the decrease in knot strength and elongation required as a suture, and to achieve significant release of hyaluronic acid.
- the average particle size of the hyaluronic acid may be in the range of 1 ⁇ m to 400 ⁇ m, for example, the average particle size of the hyaluronic acid may be in the range of 1 ⁇ m to 300 ⁇ m. It is possible to minimize the decrease in knot strength and knot elongation within the above particle size range.
- the average particle size of the hyaluronic acid is in the range of 1 ⁇ m to 300 ⁇ m, and the absorbable suture contains the hyaluronic acid in an amount of 0.5% by weight or more and 3.0% by weight or less based on the total weight of the absorbable suture.
- the absorbent polymer is composed of polydioxanone (PDO, Poly[p-dioxanone]), and the melt index (Ml) of the polydioxanone (PDO, Poly[p-dioxanone]) is 2 g / 10 min or more. It can be characterized in that the range of 16 g / 10 min or less. Within the above range, it is possible to prevent a rapid decrease in Breaking Strength Retention (BSR) 2 weeks after transplantation and to enable use as an absorbable suture.
- BSR Breaking Strength Retention
- the step of introducing the water absorbent polymer raw material into a spinning chamber at a pressure of 80 to 120 bar and a temperature range of 150 ° C. to 190 ° C., and melting the introduced water absorbent polymer while rotating a screw inside the spinning chamber wherein the mixing step is characterized in that when the water absorbent polymer is completely melted, the hyaluronic acid is added and mixed. It may be characterized by spinning in a state in which the temperature ranges from 200° C. to 200° C. and the pressure ranges from 20 bar to 60 bar.
- the absorbent polymer raw material can be melted while rotating the screw under conditions of a pressure of 80 to 120 bar and a temperature range of 150 ° C to 190 ° C in the spinning chamber, and after melting is completed, hyaluronic acid is added to mix them more evenly in the mixed raw material. Thereafter, an absorbable suture may be manufactured by performing spinning at a temperature range of 160° C. to 200° C. and a pressure range of 20 bar to 60 bar through the nozzle unit connected to the spinning chamber.
- the stretching step may include a first stretching step at a stretching ratio of 1:3 to 1:7, and a second stretching step at a stretching ratio of 1:1.1 to 1:2.
- the contracting step may be a process of adjusting the suture to contract at a constant rate while preventing excessive contraction in the process of cooling the suture after the stretching step.
- Absorbable sutures were spun by using polydioxanone (PDO, Poly[p-dioxanone]) as an absorbable polymer and mixing hyaluronic acid.
- PDO polydioxanone
- hyaluronic acid was added in a state in which polydioxanone was all melted, further mixing and melting, and then spinning was performed.
- An absorbable suture having an average diameter of 0.47 mm was prepared by varying the content of hyaluronic acid.
- knot strength and knot elongation were measured relative to the content of each hyaluronic acid, and the results are shown in Table 2 below.
- Knot strength and knot elongation were measured using a tensile strength tester (Cometech Model QC-508). The specific measurement method was to check the regulator and air pressure (about 5kg/cm 2 ) before testing using a tensile strength measuring instrument, and set the experimental conditions as shown in Table 1 below.
- Knot strength and knot elongation experiments were conducted after tying an absorbable suture, and knot elongation was measured simultaneously while measuring knot strength.
- the power of the tensile strength tester was turned on, and after warming up for about 20 minutes, the program was executed on the connected PC. Then, after confirming the gap between the grips as 200mm, if the gap is different, adjust the gap using Jog, and then open the air valve to adjust the air pressure to about 5kg/cm 2 . Thereafter, the zero point of the instrument was set, the sample was fixed to the upper and lower grips, and the knot strength and knot elongation of the sample were measured by pressing the start button. The experiment was repeated five times or more, and the measured average value was recorded and measured.
- Hyaluronic acid content (% by weight) Knot strength (N) Knot elongation (%) 0.1 57.0 34.6 0.5 56.5 35,0 1.0 57.4 35.9 2.0 58.5 36.3 3.0 56.7 34.7 4.0 42.3 22.1 5.0 36.3 19.9 10.0 18.2 10.1 20.0 8.9 6.5
- the knot strength is maintained at 40N or more up to 4.0% by weight of hyaluronic acid, and it can be confirmed that the decrease occurs to less than 40N at 5.0% by weight.
- the hyaluronic acid content is preferably less than 5% by weight, as the standard in Europe requires 39N or more. Further, more preferably, the content of hyaluronic acid is 4% by weight or less, and the content of hyaluronic acid is more preferably 3% by weight or less. It can be confirmed that it is possible to prevent a rapid decrease in knot strength and knot elongation within the above range.
- an absorbable suture having an average diameter of 0.47 mm was prepared by changing the average particle size of the injected hyaluronic acid particles while the hyaluronic acid content was fixed at 2% by weight in the total absorbable suture. Thereafter, the knot strength and knot elongation of the absorbable suture were measured in the same manner as in Experimental Example 1, and the results are shown in Table 3.
- the average particle size of hyaluronic acid is preferably 400 ⁇ m or less.
- the average particle size of hyaluronic acid is 300 ⁇ m or less.
- Absorbable sutures were spun by using polydioxanone (PDO, Poly[p-dioxanone]) as an absorbable polymer and mixing hyaluronic acid.
- Absorbable sutures with an average diameter of 0.47 mm were prepared by varying the content of hyaluronic acid relative to the total weight of the absorbable suture and the average particle size of hyaluronic acid.
- the knot strength of the absorbable suture was measured in the same manner as in Experimental Example 1, and the results are shown in Table 4 shown as
- the knot strength is prevented from falling below 40 N so that it can be used as a suture, and it can be confirmed that the range of 4.0% by weight or less is preferable. More preferably, when the content of hyaluronic acid is 3.0% by weight or less, it can be confirmed that a rapid decrease in knot strength can be prevented. In addition, it can be confirmed that the knot strength can be stably secured in the range of the average particle size of hyaluronic acid of 400 ⁇ m or less, and it can be confirmed that it is preferable to prevent a rapid decrease in knot strength in the range of 300 ⁇ m or less.
- the function as a suture can be performed while minimizing the decrease in knot strength.
- the average particle size of hyaluronic acid is in the range of 400 ⁇ m or less and the content of hyaluronic acid is less than 5.0% by weight, preferably less than 4.0% by weight, or more preferably less than 3.0%
- the function of the suture can be performed while minimizing the decrease in knot strength.
- Absorbable sutures were spun by using polydioxanone (PDO, Poly[p-dioxanone]) as an absorbable polymer and mixing hyaluronic acid.
- Absorbable sutures with an average diameter of 0.47 mm were prepared by varying the content of hyaluronic acid relative to the total weight of the absorbable suture.
- the detected amounts measured after 1 week, 3 weeks, 4 weeks, 5 weeks, 6 weeks, 7 weeks, and 8 weeks are shown in Table 5 below according to each content.
- the detection amount of hyaluronic acid was measured using a UV Spectrometer (Jasco V-700 model), and a wavelength of 260 nm that can measure the concentration of DNA was used.
- An absorbable suture using polydioxanone (PDO, Poly[p-dioxanone]) to which hyaluronic acid was not added was used as a control group used in the test.
- the test proceeded by turning on the UV Spectrometer, adjusting the zero point using Autozero, preparing a diluted solution (PBS buffer), and using the diluted solution as a blank, the absorbance was measured with a UV Spectrometer. Thereafter, the control sample (polydioxanone suture without hyaluronic acid) dissolved in the diluted solution was put in a quartz cell and measured with a UV spectrometer, and the sample mixed with the absorbable suture prepared for each hyaluronic acid content was dissolved in the diluted solution and placed in a quartz cell and measured with a UV spectrometer, and the value obtained by subtracting the absorbance of the control group from the absorbance of the sample was used as the result.
- the control sample polydioxanone suture without hyaluronic acid
- a solution in which only hyaluronic acid was dissolved was measured with a UV spectrometer to confirm the absorbance value for each concentration, and the concentration value was calculated by comparing the resultant value of the sample with reference to the absorbance value of the standard solution.
- the content of hyaluronic acid is 0.01, 0.05, and 0.1% by weight, the release of hyaluronic acid is substantially released at a very insignificant level, and the amount of release is rapidly increased at the content of 0.5% by weight compared to 0.1% by weight. Therefore, it is preferable that the content of hyaluronic acid is more than 0.1% by weight, more preferably in the range of 0.5% by weight or more, the amount of hyaluronic acid released can be relatively larger, for example, in the range of 1.0% by weight or more, more significant hyaluronic acid can be released.
- Absorbable sutures were spun by using polydioxanone (PDO, Poly[p-dioxanone]) as an absorbable polymer and mixing hyaluronic acid.
- Absorbable sutures with an average diameter of 0.47 mm were prepared by changing the melt index (MI) of polydioxanone, and breaking strength retention (BSR) was measured 2 weeks after implantation into the skin using each manufactured absorbable suture. The results are as follows. Table 6 shows.
- BSR Breaking Strength Retention
- the specific measurement method for measuring Breaking Strength Retention (BSR) after 2 weeks after implantation in the skin is to first put distilled water in a 1L Volumetric flask, add 5 BSR Tablet (Sigma aldrich Phosphate Buffered Saline Tablet), and completely dissolve using a spinbar and magnetic stirrer to prepare a buffer solution of pH 7.4. Thereafter, two samples of absorbable suture to be measured were prepared, each 3 m long, and each was placed in a 50 ml graduated centrifugal tube. Thereafter, about 40 ml of the prepared buffer solution was put into the graduated centrifuge tube so that the sample was sufficiently submerged, and the lid of the graduated centrifuge tube was closed.
- BSR Tablet Sigma aldrich Phosphate Buffered Saline Tablet
- distilled water was prepared in a shaking water bath, the temperature of the bath was set to 37 ° C ⁇ 0.3, and the shaking speed was set to 30 rpm, and the graduated centrifugal tube containing the sample was immersed in the shaking water bath. On the other hand, the knot strength was measured on the remaining one sample as day 0, and the result was recorded.
- the sample was taken out of the graduated centrifugal tube and the knot strength (EP knot) of the sample was measured using a tensile strength measuring instrument (Cometech Model QC-508).
- the measurement conditions of the tensile strength measuring instrument were sample length of 30 cm or more, grip interval of 200 mm, and speed of 300 mm/min.
- the measurement results were recorded and the knot strength retention rate was calculated based on the knot strength at day 0.
- the strength retention rate (%) is a value obtained by dividing the initial knot strength (kgf) by the knot strength (kgf) after a specific time and multiplying by 100, and the specific formula is as follows.
- Breaking Strength Retention (BSR) after 2 weeks after implantation in the skin is to confirm the strength retention in the body through an in-vitro test, which confirms the retention strength compared to the initial strength.
- BSR Breaking Strength Retention
- the strength gradually decreases as the wound heals, and the change in strength over time must be measured.
- the period required for wound healing is about 2 weeks, and the strength of the suture must be maintained within this period.
- the melting index (MI) of polydioxanone (PDO, Poly[p-dioxanone]) in the absorbable suture may be in the range of 1 g/10 min or more to 20 g/10 min or less, and preferably in the range of 2 g/10 min or more to 18 g/10 min or less.
- the melt index of polydioxanone is in the range of 2 g / 10 min or more to 16 g / 10 min or less
- the BSR value is rapidly lowered at the melt index of 18 g / 10 min compared to the BSR value.
- Absorbable sutures were spun by using polydioxanone (PDO, Poly[p-dioxanone]) as an absorbable polymer and mixing hyaluronic acid.
- Absorbable sutures with an average diameter of 0.47 mm were prepared by varying the melt index (MI) of polydioxanone (PDO, Poly[p-dioxanone]) and the content of hyaluronic acid. Breaking Strength Retention (BSR) was measured. The results of the measured BSR are shown in Table 7 below. Strong retention rate (BSR) was measured in the same manner as in Experimental Example 5.
- Hyaluronic acid content (% by weight) 0.01 0.05 0.1 0.5 1.0 3.0 5.0 10.0 MI (g/min) 2 78.0% 80.0% 76.0% 78.0% 77.0% 68.0% 65.0% 60.0% 8 75.0% 77.0% 73.0% 75.0% 75.0% 65.0% 66.0% 58.0% 10 70.0% 69.0% 68.0% 66.0% 65.0% 60.0% 61.0% 57.0% 14 69.0% 67.0% 65.0% 63.0% 65.0% 61.0% 60.0% 55.0% 16 66.0% 61.0% 63.0% 66.0% 62.0% 58.0% 53.0% 50.0% 18 58.0% 60.0% 59.0% 49.0% 45.0% 43.0% 41.0% 39.0% 20 51.0% 52.0% 48.0% 41.0% 42.0% 40.0% 39.0% 35.0% 22 43.0% 40.0% 41.0% 38.0%
- the polydioxanone may have a melt index (Melting Index: MI) in the range of 1 g/10 min or more to 20 g/10 min or less, preferably 2 g/10 min or more to 18 g/10 min or less.
- MI Melting Index
- the melt index of polydioxanone is in the range of 2 g / 10 min or more to 16 g / 10 min or less
- the BSR value is rapidly lowered at the melt index of 18 g / 10 min compared to the BSR value.
- the content of hyaluronic acid is preferably less than 5.0% by weight, more preferably less than 4.0% by weight, and more preferably less than 3.0% by weight.
- the hyaluronic acid is in the range of more than 0.1% by weight to less than 5.0% by weight, more than 0.1% by weight to less than 4.0% by weight, more than 0.1% to less than 3.0% by weight, more than 0.5% to less than 5.0% by weight, more than 0.5% to less than 4.0% by weight, more than 0.5% to less than 3.0% by weight, 1.0% by weight While satisfying the range of % or more to less than 5.0% by weight, the range of 1.0% or more to 4.0% by weight or less, or the range of 1.0% or more to 3.0% by weight or less, the melt index of polydioxanone is 2g / 10min or more to 16 It is preferable to satisfy the range of g / 10min or less.
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Abstract
Description
시험항목 | 시험횟수 | Limits Load(kgf) | Limits Extention(mm) | Speed(mm/mm) | Length(mm) |
매듭강도 | 5회 | 450 | 300 | 300 | 200 |
히알루론산 함유량(중량%) | 매듭강도(N) | 매듭신도(%) |
0.1 | 57.0 | 34.6 |
0.5 | 56.5 | 35,0 |
1.0 | 57.4 | 35.9 |
2.0 | 58.5 | 36.3 |
3.0 | 56.7 | 34.7 |
4.0 | 42.3 | 22.1 |
5.0 | 36.3 | 19.9 |
10.0 | 18.2 | 10.1 |
20.0 | 8.9 | 6.5 |
항목 | 평균입도 | |||||
50㎛ | 100㎛ | 200㎛ | 300㎛ | 400㎛ | 500㎛ | |
매듭강도(N) | 58.1 | 58.5 | 57.1 | 57.3 | 41.0 | 30.6 |
매듭신도(%) | 36.2 | 36.3 | 34.9 | 34.7 | 25.9 | 16.9 |
매듭강도(N) | 함량(중량%) | |||||||||
0.1 | 0.5 | 1.0 | 2.0 | 3.0 | 4.0 | 5.0 | 10.0 | 20.0 | ||
평균입도 (㎛) |
50 | 57.3 | 55.5 | 58.5 | 58.1 | 57.0 | 42.9 | 35.1 | 20.0 | 10.5 |
100 | 55.7 | 53.5 | 57.6 | 58.5 | 58.5 | 44.6 | 35.7 | 23.2 | 12.4 | |
200 | 54.7 | 60.0 | 56.8 | 57.1 | 57.3 | 42.1 | 36.0 | 19.1 | 11.4 | |
300 | 57.6 | 57.5 | 57.2 | 57.3 | 53.5 | 42.3 | 35.5 | 17.0 | 9.3 | |
400 | 40.1 | 40.7 | 40.2 | 41.0 | 40.7 | 30.9 | 21.5 | 13.2 | 7.4 | |
500 | 30.2 | 30.3 | 30.5 | 30.6 | 30.7 | 20.7 | 18.9 | 10.2 | 6.3 |
함유량(중량%) | 0.01 | 0.05 | 0.1 | 0.5 | 1.0 | 3.0 | 5.0 | 10.0 |
시간(주 후) | 방출량 | |||||||
1주 | 2.6 | 8.6 | 12.3 | 126.6 | 249.5 | 750.5 | 1244.4 | 2400.5 |
2주 | 4.3 | 14.3 | 20.4 | 210.1 | 413.9 | 1247.1 | 2069.5 | 4141.7 |
3주 | 4.1 | 13.8 | 19.7 | 202.9 | 399.7 | 1200.1 | 1999.0 | 3993.0 |
4주 | 3.2 | 10.6 | 15.1 | 155.5 | 306.3 | 919.0 | 1535.1 | 3070.0 |
5주 | 4.2 | 13.9 | 19.9 | 204.9 | 403.7 | 1211.0 | 2334.5 | 4110.0 |
6주 | 4.8 | 16.2 | 23.1 | 237.9 | 468.7 | 1406.3 | 2018.8 | 4688.3 |
7주 | 6.4 | 21.3 | 30.4 | 313.1 | 616.8 | 1854.5 | 3085.5 | 6008.5 |
8주 | 8.7 | 29.2 | 41.7 | 429.5 | 846.1 | 2580.0 | 4333.0 | 8500.1 |
MI(g/10min) | BSR 2주 후 (%) |
2 | 68.0 |
8 | 65.0 |
10 | 60.0 |
14 | 61.0 |
16 | 58.0 |
18 | 43.0 |
20 | 40.0 |
22 | 35.0 |
BSR 2주 후 (%) | 히알루론산 함유량(중량%) | ||||||||
0.01 | 0.05 | 0.1 | 0.5 | 1.0 | 3.0 | 5.0 | 10.0 | ||
MI (g/min) |
2 | 78.0% | 80.0% | 76.0% | 78.0% | 77.0% | 68.0% | 65.0% | 60.0% |
8 | 75.0% | 77.0% | 73.0% | 75.0% | 75.0% | 65.0% | 66.0% | 58.0% | |
10 | 70.0% | 69.0% | 68.0% | 66.0% | 65.0% | 60.0% | 61.0% | 57.0% | |
14 | 69.0% | 67.0% | 65.0% | 63.0% | 65.0% | 61.0% | 60.0% | 55.0% | |
16 | 66.0% | 61.0% | 63.0% | 66.0% | 62.0% | 58.0% | 53.0% | 50.0% | |
18 | 58.0% | 60.0% | 59.0% | 49.0% | 45.0% | 43.0% | 41.0% | 39.0% | |
20 | 51.0% | 52.0% | 48.0% | 41.0% | 42.0% | 40.0% | 39.0% | 35.0% | |
22 | 43.0% | 40.0% | 41.0% | 38.0% | 37.0% | 35.0% | 31.0% | 20.0% |
Claims (14)
- 폴리 L-락트산(PLLA, Poly[L-Lactic Acid]), 폴리락트산(PLA, Poly[Lactic Acid]), 폴리디옥사논(PDO, Poly[p-dioxanone]), 폴리카프로락톤(PCL, Poly[ε-carprolactone]), 폴리글리콜산(PGA, Poly[glycolic acid]), 폴리글리콜산 카프로락톤 (PGCL, Poly[glycolic Acid-co-ε-carprolactone), 폴리락틱코글리콜산(PLGA, Poly[L-lactic-co-glycolic Acid), 폴리 L-락트산 카프로락톤 공중합체(PLCL, Poly[L-lactide-co-ε-caprolactone]), 폴리 다이옥사논 카프로락톤 공중합체(PDCL, Poly[p-dioxanone-co-ε-caprolactone]), 및 폴리 다이옥사논 L-락트산 공중합체 (PLDA, Poly[L-lactic acid-co-p-dioxanone] 으로 이루어진 군에서 선택된 적어도 하나 이상의 재료를 포함하는 흡수성 고분자; 및상기 흡수성 고분자의 내에 함유된 히알루론산(hyaluronic acid);을 포함하고,상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.1중량% 초과 내지 5.0중량% 미만의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사.
- 제 1항에 있어서,상기 흡수성 봉합사는 모노필라멘트(monofilament)로 구성되고,상기 히알루론산은 상기 모노필라멘트 내부 및 표면에 분포되어 있는 것을 특징으로 하는 흡수성 봉합사.
- 제 1항에 있어서,상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.5중량% 이상 내지 5.0중량% 미만의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사.
- 제 1항에 있어서,상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.5중량% 이상 내지 4.0중량% 이하의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사.
- 제 1항에 있어서,상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.5중량% 이상 내지 3.0중량% 이하의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사.
- 제 1항에 있어서,상기 흡수성 봉합사는 이식 후 2주 후 강력 유지율(Breaking Strength Retention: BSR)이 40%이상 내지 80%이하의 범위인 것을 특징으로 하는 흡수성 봉합사.
- 제 1항에 있어서,상기 흡수성 고분자는 폴리디옥사논(PDO, Poly[p-dioxanone])으로 구성되고,상기 폴리디옥사논(PDO, Poly[p-dioxanone])의 용융지수(Melting Index: MI)는 2g/10min 이상 내지 16 g/10min 이하의 범위인 것을 특징으로 하는 흡수성 봉합사.
- 폴리 L-락트산(PLLA, Poly[L-Lactic Acid]), 폴리락트산(PLA, Poly[Lactic Acid]), 폴리디옥사논(PDO, Poly[p-dioxanone]), 폴리카프로락톤(PCL, Poly[ε-carprolactone]), 폴리글리콜산(PGA, Poly[glycolic acid]), 폴리글리콜산 카프로락톤 (PGCL, Poly[glycolic Acid-co-ε-carprolactone), 폴리락틱코글리콜산(PLGA, Poly[L-lactic-co-glycolic Acid), 폴리 L-락트산 카프로락톤 공중합체(PLCL, Poly[L-lactide-co-ε-caprolactone]), 폴리 다이옥사논 카프로락톤 공중합체(PDCL, Poly[p-dioxanone-co-ε-caprolactone]), 및 폴리 다이옥사논 L-락트산 공중합체 (PLDA, Poly[L-lactic acid-co-p-dioxanone] 으로 이루어진 군에서 선택된 적어도 하나 이상의 재료를 포함하는 흡수성 고분자 원료 및 분말형태의 히알루론산(hyaluronic acid)의 원료를 준비하는 단계;상기 흡수성 고분자 및 상기 히알루론산을 혼합하는 단계;상기 흡수성 고분자 및 상기 히알루론산을 방사하는 단계; 및방사된 봉합사를 연신하는 단계;를 포함하되,상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.1중량% 초과 내지 5.0중량% 미만의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사 제조방법.
- 제 8항에 있어서,상기 히알루론산의 평균입도는 1㎛ 내지 400㎛의 범위인 것을 특징으로 하는 흡수성 봉합사 제조방법.
- 제 8항에 있어서,상기 히알루론산의 평균입도는 1㎛ 내지 300㎛의 범위이고, 상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.5중량% 이상 내지 4.0중량% 이하의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사 제조방법.
- 제 8항에 있어서,상기 히알루론산의 평균입도는 1㎛ 내지 300㎛의 범위이고, 상기 흡수성 봉합사 내에 전체 중량 중 상기 히알루론산을 0.5중량% 이상 내지 3.0중량% 이하의 범위로 포함하는 것을 특징으로 하는 흡수성 봉합사 제조방법.
- 제 8항에 있어서,상기 흡수성 고분자는 폴리디옥사논(PDO, Poly[p-dioxanone])으로 구성되고,상기 폴리디옥사논(PDO, Poly[p-dioxanone])의 용융지수(Melting Index: MI)는 2g/10min 이상 내지 16 g/10min 이하의 범위인 것을 특징으로 하는 흡수성 봉합사 제조방법.
- 제 8항에 있어서,상기 혼합하는 단계 전 상기 흡수성 고분자 원료를 80 내지 120bar의 압력 및 150℃내지 190℃의 온도 범위의 방사챔버에 투입하는 단계; 및상기 방사챔버 내부의 스크류를 회전하면서 투입된 흡수성 고분자를 용융하는 단계;를 더 포함하고,상기 혼합하는 단계는 상기 흡수성 고분자가 완전히 용해되면, 상기 히알루론산을 투입하여 혼합하는 것을 특징으로 하며,상기 방사하는 단계는 상기 방사챔버에 연결된 노즐부를 160℃내지 200℃의 온도 범위 및 20 bar 내지 60 bar의 압력 범위로 조절한 상태에서 방사하는 것을 특징으로 하는 흡수성 봉합사 제조방법.
- 제 13항에 있어서,상기 연신하는 단계는 1:3 내지 1:7의 연신비로 연신하는 제 1차 연신단계, 1:1.1 내지 1:2의 연신비로 연신하는 제 2차 연신단계를 포함하는 것을 특징으로 하며,상기 연신하는 단계 이후 1:0.5 내지 1:0.9의 비율로 수축하는 단계를 더 포함하는 것을 특징으로 하는 흡수성 봉합사 제조방법.
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20160166727A1 (en) * | 2014-12-11 | 2016-06-16 | Tepha, Inc. | Methods of Orienting Multifilament Yarn and Monofilaments of Poly-4-Hydroxybutyrate and Copolymers Thereof |
KR20160107781A (ko) * | 2015-03-05 | 2016-09-19 | 주식회사 덱스레보 | 조직 고정용 필라멘트 |
KR20180109914A (ko) * | 2016-01-05 | 2018-10-08 | 아브라함 아미르 | 피부-확대용 수술 봉합물 |
KR20200007698A (ko) * | 2018-07-13 | 2020-01-22 | 주식회사 삼양바이오팜 | 피부 콜라겐 생성 촉진용 생분해성 고분자 실 필러 및 이의 제조방법 |
KR20200033487A (ko) * | 2018-09-20 | 2020-03-30 | 주식회사 지메디언스 | 기능성 봉합사 및 그 제조방법 |
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KR101784863B1 (ko) | 2015-09-03 | 2017-10-13 | (주)진우바이오 | 히알루론산염이 코팅된 고 기능성 봉합사의 제조방법 및 이로부터 제조된 고 기능성 봉합사 |
US20180221021A1 (en) * | 2017-02-08 | 2018-08-09 | Ethicon, Inc. | Braided suture with filament containing a medicant |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20160166727A1 (en) * | 2014-12-11 | 2016-06-16 | Tepha, Inc. | Methods of Orienting Multifilament Yarn and Monofilaments of Poly-4-Hydroxybutyrate and Copolymers Thereof |
KR20160107781A (ko) * | 2015-03-05 | 2016-09-19 | 주식회사 덱스레보 | 조직 고정용 필라멘트 |
KR20180109914A (ko) * | 2016-01-05 | 2018-10-08 | 아브라함 아미르 | 피부-확대용 수술 봉합물 |
KR20200007698A (ko) * | 2018-07-13 | 2020-01-22 | 주식회사 삼양바이오팜 | 피부 콜라겐 생성 촉진용 생분해성 고분자 실 필러 및 이의 제조방법 |
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