JPS6338463A - Surgical suturing yarn - Google Patents
Surgical suturing yarnInfo
- Publication number
- JPS6338463A JPS6338463A JP61183000A JP18300086A JPS6338463A JP S6338463 A JPS6338463 A JP S6338463A JP 61183000 A JP61183000 A JP 61183000A JP 18300086 A JP18300086 A JP 18300086A JP S6338463 A JPS6338463 A JP S6338463A
- Authority
- JP
- Japan
- Prior art keywords
- suture
- aliphatic polyester
- flexibility
- aromatic polyester
- polyester
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
- 125000003118 aryl group Chemical group 0.000 claims description 19
- 229920003232 aliphatic polyester Polymers 0.000 claims description 18
- 229920000728 polyester Polymers 0.000 claims description 14
- 229920001059 synthetic polymer Polymers 0.000 claims description 4
- 210000004872 soft tissue Anatomy 0.000 description 11
- 238000000034 method Methods 0.000 description 9
- LYCAIKOWRPUZTN-UHFFFAOYSA-N Ethylene glycol Chemical compound OCCO LYCAIKOWRPUZTN-UHFFFAOYSA-N 0.000 description 5
- 210000004204 blood vessel Anatomy 0.000 description 5
- 230000007423 decrease Effects 0.000 description 5
- KKEYFWRCBNTPAC-UHFFFAOYSA-N Terephthalic acid Chemical compound OC(=O)C1=CC=C(C(O)=O)C=C1 KKEYFWRCBNTPAC-UHFFFAOYSA-N 0.000 description 4
- 125000002947 alkylene group Chemical group 0.000 description 4
- WERYXYBDKMZEQL-UHFFFAOYSA-N butane-1,4-diol Chemical compound OCCCCO WERYXYBDKMZEQL-UHFFFAOYSA-N 0.000 description 4
- 125000004432 carbon atom Chemical group C* 0.000 description 4
- 229920001577 copolymer Polymers 0.000 description 4
- 238000002425 crystallisation Methods 0.000 description 4
- 230000008025 crystallization Effects 0.000 description 4
- 210000001519 tissue Anatomy 0.000 description 4
- DNIAPMSPPWPWGF-UHFFFAOYSA-N Propylene glycol Chemical compound CC(O)CO DNIAPMSPPWPWGF-UHFFFAOYSA-N 0.000 description 3
- 238000006065 biodegradation reaction Methods 0.000 description 3
- 239000008280 blood Substances 0.000 description 3
- 210000004369 blood Anatomy 0.000 description 3
- 150000002596 lactones Chemical class 0.000 description 3
- -1 polypropylene Polymers 0.000 description 3
- 238000007142 ring opening reaction Methods 0.000 description 3
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical group [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 2
- PEDCQBHIVMGVHV-UHFFFAOYSA-N Glycerine Chemical compound OCC(O)CO PEDCQBHIVMGVHV-UHFFFAOYSA-N 0.000 description 2
- AEMRFAOFKBGASW-UHFFFAOYSA-N Glycolic acid Chemical compound OCC(O)=O AEMRFAOFKBGASW-UHFFFAOYSA-N 0.000 description 2
- OFOBLEOULBTSOW-UHFFFAOYSA-N Malonic acid Chemical compound OC(=O)CC(O)=O OFOBLEOULBTSOW-UHFFFAOYSA-N 0.000 description 2
- 239000004721 Polyphenylene oxide Substances 0.000 description 2
- 229910052799 carbon Inorganic materials 0.000 description 2
- 210000001105 femoral artery Anatomy 0.000 description 2
- 150000002334 glycols Chemical class 0.000 description 2
- 125000002887 hydroxy group Chemical group [H]O* 0.000 description 2
- QQVIHTHCMHWDBS-UHFFFAOYSA-N isophthalic acid Chemical compound OC(=O)C1=CC=CC(C(O)=O)=C1 QQVIHTHCMHWDBS-UHFFFAOYSA-N 0.000 description 2
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 description 2
- 125000002496 methyl group Chemical group [H]C([H])([H])* 0.000 description 2
- XNGIFLGASWRNHJ-UHFFFAOYSA-N phthalic acid Chemical compound OC(=O)C1=CC=CC=C1C(O)=O XNGIFLGASWRNHJ-UHFFFAOYSA-N 0.000 description 2
- 229920000570 polyether Polymers 0.000 description 2
- 229920000642 polymer Polymers 0.000 description 2
- 238000009987 spinning Methods 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- PAPBSGBWRJIAAV-UHFFFAOYSA-N ε-Caprolactone Chemical compound O=C1CCCCCO1 PAPBSGBWRJIAAV-UHFFFAOYSA-N 0.000 description 2
- RKDVKSZUMVYZHH-UHFFFAOYSA-N 1,4-dioxane-2,5-dione Chemical compound O=C1COC(=O)CO1 RKDVKSZUMVYZHH-UHFFFAOYSA-N 0.000 description 1
- YNOPIKHMZIOWHS-UHFFFAOYSA-N 3,5-bis(trifluoromethyl)benzamide Chemical compound NC(=O)C1=CC(C(F)(F)F)=CC(C(F)(F)F)=C1 YNOPIKHMZIOWHS-UHFFFAOYSA-N 0.000 description 1
- 229920000954 Polyglycolide Polymers 0.000 description 1
- 239000004743 Polypropylene Substances 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 125000003178 carboxy group Chemical group [H]OC(*)=O 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 238000009833 condensation Methods 0.000 description 1
- 230000005494 condensation Effects 0.000 description 1
- 150000001991 dicarboxylic acids Chemical class 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000002349 favourable effect Effects 0.000 description 1
- 235000011187 glycerol Nutrition 0.000 description 1
- XXMIOPMDWAUFGU-UHFFFAOYSA-N hexane-1,6-diol Chemical compound OCCCCCCO XXMIOPMDWAUFGU-UHFFFAOYSA-N 0.000 description 1
- 230000007062 hydrolysis Effects 0.000 description 1
- 238000006460 hydrolysis reaction Methods 0.000 description 1
- WGCNASOHLSPBMP-UHFFFAOYSA-N hydroxyacetaldehyde Natural products OCC=O WGCNASOHLSPBMP-UHFFFAOYSA-N 0.000 description 1
- 235000014655 lactic acid Nutrition 0.000 description 1
- 239000004310 lactic acid Substances 0.000 description 1
- JJTUDXZGHPGLLC-UHFFFAOYSA-N lactide Chemical compound CC1OC(=O)C(C)OC1=O JJTUDXZGHPGLLC-UHFFFAOYSA-N 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000002074 melt spinning Methods 0.000 description 1
- 238000002844 melting Methods 0.000 description 1
- 230000008018 melting Effects 0.000 description 1
- 238000002156 mixing Methods 0.000 description 1
- RXOHFPCZGPKIRD-UHFFFAOYSA-N naphthalene-2,6-dicarboxylic acid Chemical compound C1=C(C(O)=O)C=CC2=CC(C(=O)O)=CC=C21 RXOHFPCZGPKIRD-UHFFFAOYSA-N 0.000 description 1
- 229920005615 natural polymer Polymers 0.000 description 1
- 206010033675 panniculitis Diseases 0.000 description 1
- 238000012643 polycondensation polymerization Methods 0.000 description 1
- 239000004633 polyglycolic acid Substances 0.000 description 1
- 229920001155 polypropylene Polymers 0.000 description 1
- 229920000874 polytetramethylene terephthalate Polymers 0.000 description 1
- 238000010791 quenching Methods 0.000 description 1
- 230000000171 quenching effect Effects 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- 238000007151 ring opening polymerisation reaction Methods 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 210000004304 subcutaneous tissue Anatomy 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 229920002994 synthetic fiber Polymers 0.000 description 1
- 239000012209 synthetic fiber Substances 0.000 description 1
Landscapes
- Materials For Medical Uses (AREA)
Abstract
(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Abstract] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】
［産業上の利用分野コ
本発明は芳香族ポリエステルと脂肪族ポリエステルとを
共重合させたポリエステル共重合体の延伸モノフィラメ
ントからなる外科用縫合糸に関する。DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to a surgical suture consisting of a drawn monofilament of a polyester copolymer obtained by copolymerizing an aromatic polyester and an aliphatic polyester.
［従来の技術］
従来から縫合糸として、絹糸のような天然高分子からポ
リプロピレンなどの合成高分子まで数多くの素材の糸が
使用されている。[Prior Art] Threads made of many materials have been used as suture threads, ranging from natural polymers such as silk threads to synthetic polymers such as polypropylene.
近年、医学の進歩により、精巧かつ複雑な外科手術に対
応した優れた性質を有する縫合糸が求められている。BACKGROUND ART In recent years, with advances in medicine, there is a demand for sutures with excellent properties that can be used in delicate and complex surgical operations.
このような縫合糸の１つに、生体軟組織（とくに血管壁
や皮膚など）の応力−歪曲線に近似した良好な柔軟性を
有し、かつ生分解性のモノフィラメントがあげられる。One such suture is a biodegradable monofilament that has good flexibility that approximates the stress-strain curve of biological soft tissues (particularly blood vessel walls, skin, etc.).
縫合糸の機能は切れた組織を充分に治癒するまで結合し
、かつ保持することあるいは保持期間中の動作や運動の
結果としての分離を防ぐことにあるから、縫合部の組織
が完全に治癒したのちには縫合糸自体は生分解を受けて
強度が低下することが好ましい。生分解性を宵し、かつ
吸収性を釘するこのような縫合糸としては、ポリグリコ
ール酸やグリコール酸と乳酸との共重合体などからの縫
合糸が臨床に使用されているが、これらは非常に硬いた
め、その使用範囲が限定されている。The function of sutures is to bind and hold the torn tissue together until it has fully healed, or to prevent separation as a result of movement or movement during the holding period, so the tissue at the suture site has completely healed. Later on, the suture itself preferably undergoes biodegradation and its strength decreases. As such sutures that are biodegradable and absorbable, sutures made of polyglycolic acid or copolymers of glycolic acid and lactic acid are used clinically; Because it is very hard, its range of use is limited.
一方、米国特許第４２２４９４６号明細書には、芳香族
ポリエステルをハードセグメントとし、ポリエーテルを
ソフトセグメントにしたポリエステル−ポリエーテル共
重合体を延伸してなる柔軟性に富んだ縫合糸が開示され
ているが、この縫合糸は生分解性を有さない。On the other hand, U.S. Pat. No. 4,224,946 discloses a highly flexible suture made by drawing a polyester-polyether copolymer with aromatic polyester as a hard segment and polyether as a soft segment. However, this suture is not biodegradable.
［発明が解決しようとする問題点］
本発明は、生分解性を有するばあいには柔軟性が不足し
、柔軟性ををするばあいには生分解性が不足するという
従来の縫合糸における問題点を解消した、生体軟組織の
応力−歪曲線に近似した柔軟性を有し、かつ生分解性を
有する新規な縫合糸を提供することを目的としてなされ
たものである。[Problems to be Solved by the Invention] The present invention solves the problem that conventional sutures lack flexibility when they are biodegradable, and lack biodegradability when they are flexible. The purpose of this invention is to provide a novel suture that solves the problems, has flexibility that approximates the stress-strain curve of biological soft tissue, and is biodegradable.
［問題点を解決するための手段］
本発明は、ハードセグメントとして芳香族ポリエステル
部分を含有し、ソフトセグメントとして生分解性のある
脂肪族ポリエステル部分を含有芳香族ポリエステル−脂
肪族ポリエステル共重合体を延伸して縫合糸を製造する
と、生体軟組織の応力−歪曲線に近似した柔軟性を有す
る縫合糸かえられることが見出されたことによりなされ
たものであり、合成高分子の延伸モノフィラメントより
なる縫合糸において、合成高分子が芳香族ポリエステル
部分をハードセグメントとし、脂肪族ポリエステル部分
をソフトセグメントとして存する芳香族ポリエステル−
脂肪族ポリエステル共重合体であることを特徴とする外
科用縫合糸に関する。[Means for Solving the Problems] The present invention provides an aromatic polyester-aliphatic polyester copolymer containing an aromatic polyester portion as a hard segment and a biodegradable aliphatic polyester portion as a soft segment. This was done based on the discovery that when a suture is produced by drawing it, the suture can have a flexibility that approximates the stress-strain curve of biological soft tissues. In the yarn, an aromatic polyester in which the synthetic polymer exists as a hard segment in the aromatic polyester part and as a soft segment in the aliphatic polyester part.
The present invention relates to a surgical suture thread characterized by being made of an aliphatic polyester copolymer.
［実施例］
本発明における芳香族ポリエステル部分とは、一般式（
１）：
％式％（１）
（式中、Ａは芳香族ジカルボン酸から２個のカルボキシ
ル基を除いた基、Ｒは炭素数２〜６のアルキレン基、ｎ
は１以上の整数を表わす）で定義されるもの、すなわち
、芳香族ジカルボン酸またはそのエステル形成同等物と
短鎖グリコール類とからなるポリエステル部分である。[Example] The aromatic polyester moiety in the present invention has the general formula (
1): %Formula%(1) (In the formula, A is a group obtained by removing two carboxyl groups from an aromatic dicarboxylic acid, R is an alkylene group having 2 to 6 carbon atoms, n
represents an integer of 1 or more), that is, a polyester moiety consisting of an aromatic dicarboxylic acid or its ester-forming equivalent and a short chain glycol.
前記芳香族ジカルボン酸としては、たとえばテレフタル
酸、イソフタル酸、フタル酸、４，４゜−ビフェニルジ
カルボン酸、４．４−スルホニルジ安息香酸、２，６−
ナフタリンジカルボン酸などが用いられつる。縫合糸と
しての加工性がよく、抗張力が強いという面からは、こ
れらのうちでもテレフタル酸が好ましい。Examples of the aromatic dicarboxylic acids include terephthalic acid, isophthalic acid, phthalic acid, 4,4°-biphenyldicarboxylic acid, 4,4-sulfonyldibenzoic acid, and 2,6-
Naphthalene dicarboxylic acid is used. Among these, terephthalic acid is preferred from the viewpoint of good workability as a suture thread and strong tensile strength.
前記短鎖グリコール類としては、たとえばエチレングリ
コール、プロピレングリコール、１．４−ブタンジオー
ル、ヘキサメチレングリコールなどがあげられる。結晶
化速度を速くし、紡糸性や抗張力を向上させるためには
、これらのうちでも１．４−ブタンジオールが好ましい
。Examples of the short chain glycols include ethylene glycol, propylene glycol, 1,4-butanediol, and hexamethylene glycol. Among these, 1,4-butanediol is preferred in order to increase the crystallization rate and improve spinnability and tensile strength.
本発明における脂肪族ポリエステル部分は実質的に一般
式（Ｚ：
−Ｏ−Ｃ−Ｒ−−（２）
（式中、Ｒ′は炭素′＃！！、１〜８の直鎖のアルキレ
ン基または側鎖にメチル基ををするアルキレン基を表わ
す）を繰返し単位とし、分子量が４００〜２０，０００
でＴｇが室温よりも低く、生分解性を有するものである
。縫合糸として好ましい力学的性質を有するようにする
という面からすると、脂肪族ポリエステル部分はさらに
分子ｆｉ ５００〜６０００であるのが好ましく、とく
に ５００〜３００ｏであるのが好ましい。分子量が４
００未満になるとえられる縫合糸の柔軟性が不足し、分
子量が２０．０００をこえると抗張力が充分でなくなる
傾向にある。The aliphatic polyester moiety in the present invention substantially has the general formula (Z: -O-C-R--(2) (wherein R' is a carbon'#!!, a linear alkylene group having 1 to 8 carbon atoms, or (representing an alkylene group with a methyl group on the side chain) as a repeating unit, and the molecular weight is 400 to 20,000.
It has a Tg lower than room temperature and is biodegradable. From the viewpoint of having favorable mechanical properties as a suture thread, the aliphatic polyester portion preferably has a molecular fi of 500 to 6,000, particularly preferably 500 to 300o. molecular weight is 4
If the molecular weight is less than 20,000, the suture will lack flexibility, and if the molecular weight exceeds 20,000, the tensile strength will tend to be insufficient.
一般にＲ′の炭素数が小さくなると加水分解速度が速く
なり、かつ結晶性が増加し、柔軟性が低下する傾向にあ
り、Ｒ′の炭素数が多くなると逆に生分解速度が遅くな
り、かつ柔軟性が増加する傾向にある。Ｒ′は側鎖にメ
チル基を含んでいてもよいが、抗張力を高めるためには
直鎖のアルキレン基であるのが好ましい。In general, as the number of carbon atoms in R' decreases, the rate of hydrolysis increases, crystallinity increases, and flexibility tends to decrease, while as the number of carbon atoms in R' increases, the rate of biodegradation decreases, and Flexibility tends to increase. Although R' may contain a methyl group in its side chain, it is preferably a linear alkylene group in order to increase tensile strength.
該脂肪族ポリエステル部分となる脂肪族ポリエステルは
、たとえばラクトン類の開環重合、オキシ酸の縮１ｒｃ
合、ジカルボン酸とグリコールとの縮重合、グリコリド
やラクチドの開環重りなどによってうろことができる。The aliphatic polyester that becomes the aliphatic polyester moiety can be produced by, for example, ring-opening polymerization of lactones, condensation of 1rc of oxyacids, etc.
It can be produced by condensation polymerization of dicarboxylic acids and glycols, ring-opening weights of glycolide and lactide, etc.
前記柔軟性と生分解性と抗張力とのバランスを考えると
、ε−カプロラクトンの開環重合物を用いるのが好まし
い。Considering the balance between flexibility, biodegradability, and tensile strength, it is preferable to use a ring-opening polymer of ε-caprolactone.
次に本発明に用いる芳香族ポリエステル−脂肪族ポリエ
ステル共重合体について説明する。Next, the aromatic polyester-aliphatic polyester copolymer used in the present invention will be explained.
該共重合体の製法には種々の方法があり、たとえば宋国
特許第２６２３０３１号明細書に開示されているように
、脂肪族ポリエステルと芳香族ポリエステルとを溶融状
態で混合する方法、特公昭４ｇ−４１１５号公報に開示
されているように、分子両末端に水酸括を何する分子量
５００〜５０００の結晶性芳香族ポリエステルとラクト
ン類とを反応させ、ついで多官能アシル化剤で鎖延長を
行なう方法、特公昭４８−４１１６号公報に開示されて
いるように、両末端水酸基を有する高分子量の芳香族ポ
リエステルにラクトン類を反応させる方法などがある。There are various methods for producing the copolymer, such as the method of mixing aliphatic polyester and aromatic polyester in a molten state, as disclosed in Song Patent No. 2,623,031; As disclosed in Publication No. 4115, a crystalline aromatic polyester with a molecular weight of 500 to 5,000 having hydroxyl groups at both ends of the molecule is reacted with lactones, and then chain extension is performed using a polyfunctional acylating agent. As disclosed in Japanese Patent Publication No. 48-4116, there is a method in which a high molecular weight aromatic polyester having hydroxyl groups at both terminals is reacted with lactones.
本発明に用いる芳香族ポリエステル−脂肪族ポリエステ
ル共重合体は、どのような方法で製造してもよいが、脂
肪族ポリエステル部分の含自゛瓜、すなわちソフトセグ
メント比率は１０〜８０重ｕ ｑ６が好ましい。縫合糸
の柔軟性と抗張力のバランスや生分解性の速度とを考え
あわせると、さらにソフトセグメント比率が２０〜６０
重量％であるのが好ましく、とくにソフトセグメント比
率が２５〜５０重二％であるのが好ましい。ソフトセグ
メント比率が１０重量９６未満では柔軟性や生分解性が
充分でなく、ソフトセグメント比率が８０重瓜％をこえ
ると、抗張力が劣ったり結晶化速度が遅くなったりして
、紡糸や延伸が困難になりがちである。The aromatic polyester-aliphatic polyester copolymer used in the present invention may be produced by any method, but the carbon content of the aliphatic polyester portion, that is, the soft segment ratio is 10 to 80 wt. preferable. Considering the balance between suture flexibility and tensile strength and the speed of biodegradation, the soft segment ratio can be further increased from 20 to 60.
The soft segment ratio is preferably 25 to 50% by weight, particularly preferably 25 to 50% by weight. If the soft segment ratio is less than 10% by weight, the flexibility and biodegradability will not be sufficient, and if the soft segment ratio exceeds 80% by weight, the tensile strength will be poor and the crystallization rate will be slow, making spinning and drawing difficult. This tends to be difficult.
ソフトセグメント比率が高くなるにつれて結晶化速度は
遅くなる傾向にあるので、結晶化促進剤を添加してもよ
い。Since the crystallization rate tends to slow down as the soft segment ratio increases, a crystallization promoter may be added.
本発明の縫合糸を製造する際に共重合体を紡糸する方法
としては、たとえば通常の合成繊維の溶融紡糸法などが
あげられ、このような方法と同様のノブ法で行なえばよ
い。すなわち、共重合体からなる樹脂を溶融して押出し
、急冷後延伸せしめるというような方法である。このよ
うにして生分解性および生体組織に近似した柔軟性を何
する縫合糸が製造される。Examples of the method for spinning the copolymer when producing the suture of the present invention include a conventional melt spinning method for synthetic fibers, and a knob method similar to such a method may be used. That is, the method involves melting and extruding a resin made of a copolymer, quenching it, and then stretching it. In this way, a suture is produced that is biodegradable and has a flexibility that approximates living tissue.
ソフトセグメント比率によって最適な延伸倍率は変化す
るので、−概に延伸倍率を決定することはできないが、
この延伸によって分子は強く配向し、生体軟組織に近似
した柔軟性と縫合糸として充分に強い抗張力が付与され
る。前記延伸倍率は、通常３〜１５倍であり、さらに５
〜１２倍、とくに６〜ＩＯ倍である。延伸倍率が３倍侵
満になると抗張力が不足し、１５倍をこえると柔軟性に
劣る傾向にある。Since the optimal stretching ratio changes depending on the soft segment ratio, it is not possible to determine the stretching ratio in general.
This stretching strongly orients the molecules, giving it flexibility similar to that of biological soft tissue and a tensile strength strong enough to be used as a suture. The stretching ratio is usually 3 to 15 times, and further 5 times.
~12 times, especially 6-IO times. When the stretching ratio is 3 times, the tensile strength is insufficient, and when the stretching ratio exceeds 15 times, the flexibility tends to be poor.
本明細書にいう生体軟組織に近似した柔軟性とは歪が１
０〜５０？６の範囲のある歪までは小さい弾性率を示し
、その歪をこえると急激に高い弾性率を示す応力−歪曲
線を何することを意味する。In this specification, flexibility similar to biological soft tissue means that the strain is 1
What is meant by a stress-strain curve that shows a small modulus of elasticity up to a certain strain in the range of 0 to 50?6, and suddenly shows a high modulus of elasticity beyond that strain.
次に実施例に基づき本発明の詳細な説明する。Next, the present invention will be explained in detail based on examples.
実施例１
ε−カプロラクトンの開環重合物からなる脂肪族ポリエ
ステルをソフトセグメントとして３５’ｕｔ％含有せし
め、ポリ（テトラメチレンテレフタレート）からなる芳
香族ポリエステルをノ１−ドセグメントとして６５重量
％含釘せしめた芳香族ポリエステル−脂肪族ポリエステ
ル共重合体を２２０〜２４０°Ｃで１５ｍ／分の速度で
溶融紡糸した。紡糸した糸を６０°Ｃの水で急冷したの
ち、９０℃の水中で４倍に延伸し、ついでｌ ２０ ’
Ｃのグリセリン浴中で２倍に延伸した。えられた糸は直
径 ０．１２＋ｎ＋ｎであった。Example 1 An aliphatic polyester consisting of a ring-opening polymer of ε-caprolactone was contained in an amount of 35'ut% as a soft segment, and an aromatic polyester consisting of poly(tetramethylene terephthalate) was contained as a node segment in an amount of 65'ut%. The resulting aromatic polyester-aliphatic polyester copolymer was melt-spun at 220-240°C at a speed of 15 m/min. The spun yarn was quenched with water at 60°C, then stretched 4 times in water at 90°C, and then 120'
It was stretched twice in a glycerin bath of C. The resulting thread had a diameter of 0.12+n+n.
島原オートグラフｌ５−２０００を用いて測定したこの
糸の直線時および結節時の抗張力と伸びとを第１表に、
応力−歪曲線を第１図に示す。Table 1 shows the tensile strength and elongation of this yarn when it is straight and when it is knotted, as measured using Shimabara Autograph 15-2000.
The stress-strain curve is shown in FIG.
［以下余白］
第 １ 表
この糸を用いて雑種成人の大腿動脈の縫合および大腿動
脈の周囲の皮下組織を縫合したところ、血管壁や生体軟
組織に過剰な力をかけたり、あるいはこれらの組織を切
ったりすることなく、作業性よく縫合できた。とくに血
管の縫合では縫合部の密着性がよく、縫合部に血液を流
し始めた直後の血液の漏れが非常に少なかった。[Margins below] Table 1 When this thread was used to suture the femoral artery of a mongrel adult and the subcutaneous tissue surrounding the femoral artery, excessive force was applied to the blood vessel wall and soft tissues of the living body, or these tissues were It was possible to suture with good workability without cutting. In particular, when suturing blood vessels, the sutured area had good adhesion, and there was very little blood leakage immediately after blood began to flow through the sutured area.
この糸を犬の皮下に１年間埋入したところ、第２表に示
す抗張力と伸びとを示し、生分解性であることがわかっ
た。When this thread was implanted under the skin of a dog for one year, it showed the tensile strength and elongation shown in Table 2, and was found to be biodegradable.
第 ２ 表
［発明の効果］
本発明の縫合糸は、ハードセグメントが芳香族ポリエス
テルでソフトセグメントが生分解性のある脂肪族ポリエ
ステルであるため、生分解性ををする。また延伸するこ
とにより、生１体軟組織の応力−歪曲線に近似した柔軟
性を有するようにしうる。従って、本発明の縫合糸を用
いて血管などの生体軟組織の縫合を行なうと、生体軟組
織に無理な応力を加えたり生体軟組織を切ったりするこ
となく、作業性よく縫合しうる。Table 2 [Effects of the Invention] The suture of the present invention is biodegradable because the hard segment is an aromatic polyester and the soft segment is a biodegradable aliphatic polyester. Furthermore, by stretching, it can be made to have flexibility that approximates the stress-strain curve of living soft tissue. Therefore, when suturing biological soft tissues such as blood vessels using the suture thread of the present invention, suturing can be performed with good workability without applying unreasonable stress to the biological soft tissue or cutting the biological soft tissue.
とくに血管の縫合では血流再開直後の縫合部からの血液
の漏れが少ない。また本発明の縫合糸は生分解性である
ため、縫合部が冶癒したのちには１合糸の抗張力が低下
し、生体軟組織に縫合糸としての余分な応力を与えない
。In particular, when suturing blood vessels, there is little blood leakage from the sutured portion immediately after blood flow is resumed. Furthermore, since the suture of the present invention is biodegradable, the tensile strength of the suture decreases after the suture is healed, and no unnecessary stress is applied to biological soft tissue as a suture.
第１図は実施例１でえられた本発明の外科用縫合糸の応
力−歪曲線を示すグラフである。
特許出願人 鐘淵化学工業株式会社
才１図
歪 （ｚ）FIG. 1 is a graph showing the stress-strain curve of the surgical suture of the present invention obtained in Example 1. Patent applicant: Kanekabuchi Chemical Industry Co., Ltd. (z)
Claims (1)
において、合成高分子が芳香族ポリエステル部分をハー
ドセグメントとし、脂肪族ポリエステル部分をソフトセ
グメントとして有する芳香族ポリエステル−脂肪族ポリ
エステル共重合体であることを特徴とする外科用縫合糸
。1. A suture made of a drawn monofilament of a synthetic polymer, characterized in that the synthetic polymer is an aromatic polyester-aliphatic polyester copolymer having an aromatic polyester portion as a hard segment and an aliphatic polyester portion as a soft segment. and surgical sutures.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61183000A JPS6338463A (en) | 1986-08-04 | 1986-08-04 | Surgical suturing yarn |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61183000A JPS6338463A (en) | 1986-08-04 | 1986-08-04 | Surgical suturing yarn |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS6338463A true JPS6338463A (en) | 1988-02-19 |
| JPH0333026B2 JPH0333026B2 (en) | 1991-05-15 |
Family
ID=16128002
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP61183000A Granted JPS6338463A (en) | 1986-08-04 | 1986-08-04 | Surgical suturing yarn |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS6338463A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH10229A (en) * | 1996-04-19 | 1998-01-06 | Dainippon Ink & Chem Inc | Slow-releasable bioactive and bioabsorbable organic-inorganic compounded material having bone inducing or bone conducting function |
| EP0637642A4 (en) * | 1993-01-07 | 1998-12-16 | Unitika Ltd | Binder fiber and nonwoven fabric produced therefrom. |
| JP2011524949A (en) * | 2008-06-20 | 2011-09-08 | ディーエスエム アイピー アセッツ ビー．ブイ． | Ultra high molecular weight polyethylene yarn |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS57119754A (en) * | 1980-12-22 | 1982-07-26 | Ethicon Inc | Thread for high compliance monofilament operation consisting of poly (tetramethylene terephthalate-core (2-alkenyl or alkyl) succinate) |
-
1986
- 1986-08-04 JP JP61183000A patent/JPS6338463A/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS57119754A (en) * | 1980-12-22 | 1982-07-26 | Ethicon Inc | Thread for high compliance monofilament operation consisting of poly (tetramethylene terephthalate-core (2-alkenyl or alkyl) succinate) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0637642A4 (en) * | 1993-01-07 | 1998-12-16 | Unitika Ltd | Binder fiber and nonwoven fabric produced therefrom. |
| JPH10229A (en) * | 1996-04-19 | 1998-01-06 | Dainippon Ink & Chem Inc | Slow-releasable bioactive and bioabsorbable organic-inorganic compounded material having bone inducing or bone conducting function |
| JP2011524949A (en) * | 2008-06-20 | 2011-09-08 | ディーエスエム アイピー アセッツ ビー．ブイ． | Ultra high molecular weight polyethylene yarn |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0333026B2 (en) | 1991-05-15 |
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