JPH0369543B2 - - Google Patents
Info
- Publication number
- JPH0369543B2 JPH0369543B2 JP61174526A JP17452686A JPH0369543B2 JP H0369543 B2 JPH0369543 B2 JP H0369543B2 JP 61174526 A JP61174526 A JP 61174526A JP 17452686 A JP17452686 A JP 17452686A JP H0369543 B2 JPH0369543 B2 JP H0369543B2
- Authority
- JP
- Japan
- Prior art keywords
- bioprosthesis
- fibers
- yarn
- tube
- covering yarn
- 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.)
- Expired - Lifetime
Links
- 239000000835 fiber Substances 0.000 claims description 36
- 229920001410 Microfiber Polymers 0.000 claims description 33
- 238000000034 method Methods 0.000 claims description 13
- 239000000463 material Substances 0.000 claims description 10
- 238000009941 weaving Methods 0.000 claims description 10
- 239000012530 fluid Substances 0.000 claims description 9
- 238000009940 knitting Methods 0.000 claims description 7
- 238000004519 manufacturing process Methods 0.000 claims description 7
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 6
- 238000009954 braiding Methods 0.000 claims description 3
- 238000009835 boiling Methods 0.000 claims description 2
- 210000004204 blood vessel Anatomy 0.000 description 10
- 239000002473 artificial blood Substances 0.000 description 9
- 230000000694 effects Effects 0.000 description 8
- 239000004744 fabric Substances 0.000 description 7
- 229920000642 polymer Polymers 0.000 description 7
- 229920000728 polyester Polymers 0.000 description 6
- 238000012545 processing Methods 0.000 description 5
- QQVIHTHCMHWDBS-UHFFFAOYSA-N isophthalic acid Chemical compound OC(=O)C1=CC=CC(C(O)=O)=C1 QQVIHTHCMHWDBS-UHFFFAOYSA-N 0.000 description 4
- 239000003658 microfiber Substances 0.000 description 4
- -1 polytetrafluoroethylene Polymers 0.000 description 4
- LYCAIKOWRPUZTN-UHFFFAOYSA-N Ethylene glycol Chemical compound OCCO LYCAIKOWRPUZTN-UHFFFAOYSA-N 0.000 description 3
- 239000004793 Polystyrene Substances 0.000 description 3
- 239000007788 liquid Substances 0.000 description 3
- 229920002223 polystyrene Polymers 0.000 description 3
- 239000004952 Polyamide Substances 0.000 description 2
- KKEYFWRCBNTPAC-UHFFFAOYSA-N Terephthalic acid Chemical compound OC(=O)C1=CC=C(C(O)=O)C=C1 KKEYFWRCBNTPAC-UHFFFAOYSA-N 0.000 description 2
- 230000003187 abdominal effect Effects 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 229920002647 polyamide Polymers 0.000 description 2
- 229920000139 polyethylene terephthalate Polymers 0.000 description 2
- 239000005020 polyethylene terephthalate Substances 0.000 description 2
- 238000012805 post-processing Methods 0.000 description 2
- 238000004080 punching Methods 0.000 description 2
- 238000009987 spinning Methods 0.000 description 2
- 239000007921 spray Substances 0.000 description 2
- 201000004384 Alopecia Diseases 0.000 description 1
- 102000008186 Collagen Human genes 0.000 description 1
- 108010035532 Collagen Proteins 0.000 description 1
- 206010019909 Hernia Diseases 0.000 description 1
- DGAQECJNVWCQMB-PUAWFVPOSA-M Ilexoside XXIX Chemical compound C[C@@H]1CC[C@@]2(CC[C@@]3(C(=CC[C@H]4[C@]3(CC[C@@H]5[C@@]4(CC[C@@H](C5(C)C)OS(=O)(=O)[O-])C)C)[C@@H]2[C@]1(C)O)C)C(=O)O[C@H]6[C@@H]([C@H]([C@@H]([C@H](O6)CO)O)O)O.[Na+] DGAQECJNVWCQMB-PUAWFVPOSA-M 0.000 description 1
- 244000089486 Phragmites australis subsp australis Species 0.000 description 1
- 235000014676 Phragmites communis Nutrition 0.000 description 1
- 239000004698 Polyethylene Substances 0.000 description 1
- 239000004372 Polyvinyl alcohol Substances 0.000 description 1
- XSTXAVWGXDQKEL-UHFFFAOYSA-N Trichloroethylene Chemical group ClC=C(Cl)Cl XSTXAVWGXDQKEL-UHFFFAOYSA-N 0.000 description 1
- 238000004026 adhesive bonding Methods 0.000 description 1
- 230000003872 anastomosis Effects 0.000 description 1
- 230000000747 cardiac effect Effects 0.000 description 1
- 229920001436 collagen Polymers 0.000 description 1
- 238000002788 crimping Methods 0.000 description 1
- 230000002950 deficient Effects 0.000 description 1
- 230000008021 deposition Effects 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 208000024963 hair loss Diseases 0.000 description 1
- 230000003676 hair loss Effects 0.000 description 1
- 210000003709 heart valve Anatomy 0.000 description 1
- 239000012535 impurity Substances 0.000 description 1
- 230000014759 maintenance of location Effects 0.000 description 1
- 230000013011 mating Effects 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 229920000573 polyethylene Polymers 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 229920001343 polytetrafluoroethylene Polymers 0.000 description 1
- 239000004810 polytetrafluoroethylene Substances 0.000 description 1
- 229920002451 polyvinyl alcohol Polymers 0.000 description 1
- 238000003672 processing method Methods 0.000 description 1
- 238000007665 sagging Methods 0.000 description 1
- 238000009958 sewing Methods 0.000 description 1
- 238000010008 shearing Methods 0.000 description 1
- 229910052708 sodium Inorganic materials 0.000 description 1
- 239000011734 sodium Substances 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 150000003457 sulfones Chemical class 0.000 description 1
- 210000000115 thoracic cavity Anatomy 0.000 description 1
- 238000007631 vascular surgery Methods 0.000 description 1
- 239000002699 waste material Substances 0.000 description 1
- 229920003169 water-soluble polymer Polymers 0.000 description 1
Landscapes
- Materials For Medical Uses (AREA)
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、人工血管やパツチ等に代表される生
体用補綴物およびその製法に関するものである。DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to a bioprosthesis represented by an artificial blood vessel, a patch, etc., and a method for manufacturing the same.
〔従来の技術〕
従来の織編物から成る生体用補綴物は、縫合
性、耐ほつれ性、柔軟性などの特性に問題があ
り、また生体適合性の点でも多くの問題があつ
た。[Prior Art] Conventional bioprosthetics made of woven or knitted fabrics have problems in properties such as sutureability, fraying resistance, and flexibility, and also have many problems in terms of biocompatibility.
本発明者らは、上記問題点の抜本的改善を行な
うため、鋭意検討を進め極細繊維を用いることに
より、また更に高圧流体処理を行なうことにより
上記問題点を飛躍的に改善し、特開昭60−77764
号公報、特開昭61−92666号公報で開示してきた。 In order to fundamentally improve the above-mentioned problems, the inventors of the present invention have carried out intensive studies and have dramatically improved the above-mentioned problems by using ultra-fine fibers and by further performing high-pressure fluid treatment. 60−77764
It has been disclosed in Japanese Patent Application Laid-open No. 61-92666.
しかし、これら一連の研究を更に深く追及する
ことによつて、種々のあらたな問題点のあること
が判つた。
However, by pursuing these series of studies more deeply, it was discovered that there were various new problems.
第1の問題点は、多重組織からなる織編構造が
複雑であるために生じる問題点である。すなわ
ち、生体用補綴物の厚みが必要以上に厚くなるこ
とであり、そのため補綴の際の適合性例えば縫合
のしにくさや、吻合不全または小口径人工血管の
クリンプがシヤープに入らず形態保持性が付与出
来ないなどの点である。また複雑で高度な織編物
が必須であり、しかも製編織時には各種のトラブ
ル例えば製織時のオサ打込み回数が極度に多いた
めに経糸切れが発生し、場合によつては織れなく
なるなどの点である。 The first problem is a problem that arises because the woven structure consisting of multiple tissues is complex. In other words, the thickness of the bioprosthesis becomes thicker than necessary, resulting in problems with the compatibility of the prosthesis, such as difficulty in suturing, failure of anastomosis, or crimping of small-diameter artificial blood vessels that do not enter the sharp shape, resulting in poor shape retention. For example, it cannot be granted. In addition, complex and highly sophisticated woven and knitted fabrics are essential, and various problems occur during weaving, such as warp breakage occurring due to the extremely large number of reeds during weaving, and in some cases, weaving becomes impossible. .
第2の問題点は、ほつれを極めて高水準に止め
るためには通常は高圧流体処理の圧力を高め、ま
たは回数を増やす必要があり、そのために繊維特
に極細繊維はフイブリル化や破断が生じ、繊維の
脱落や強度低下などの問題があつた。 The second problem is that in order to keep fraying to a very high level, it is usually necessary to increase the pressure or increase the number of times of high-pressure fluid treatment, which causes fibers, especially microfibers, to fibrillate and break. There were problems such as falling off and a decrease in strength.
本発明者らは、上記問題点について鋭意検討を
進めた結果、ついに本発明に到達した。 The present inventors have finally arrived at the present invention as a result of intensive studies on the above-mentioned problems.
すなわち、本発明は次の構成を有する。 That is, the present invention has the following configuration.
(1) 0.9デニール以下の極細繊維を含むカバーリ
ングヤーンで構成された生体用補綴物であつ
て、該生体用補綴物を構成する極細繊維の少な
くとも一部が該ヤーン間で交絡していることを
特徴とする生体用補綴物。(1) A bioprosthesis composed of covering yarn containing ultrafine fibers of 0.9 denier or less, where at least a portion of the microfibers constituting the bioprosthesis are intertwined between the yarns. A bioprosthesis characterized by:
(2) 生体用補綴物を製造するに際し、少なくとも
下記〜の工程を含みかつ順に行なうことを
特徴とする生体用補綴物の製法。(2) A method for manufacturing a bioprosthesis, which includes at least the following steps and sequentially performed in the production of the bioprosthesis.
カバーリングヤーンを形成する工程。 Process of forming covering yarn.
該カバーリングヤーンを用いた織、編組織
または組紐組織によつて、シート状物または
チユーブ状物を形成する工程。 A step of forming a sheet-like object or a tube-like object by weaving, knitting, or braiding the covering yarn.
該シート状物またはチユーブ状物に高圧流
体処理を施す工程。 A step of subjecting the sheet-like material or tube-like material to high-pressure fluid treatment.
(3) カバーリングヤーンの芯糸が沸湯水中収縮率
10%以上を有する高収縮繊維である特許請求の
範囲第2項に記載の生体用補綴物の製法。(3) Shrinkage rate of core thread of covering yarn in boiling water
The method for producing a bioprosthesis according to claim 2, wherein the bioprosthesis is made of high shrinkage fibers having a content of 10% or more.
以下、本発明を詳細に説明する。 The present invention will be explained in detail below.
本発明でいう生体用補綴物とは、例えば胸部血
管外科手術における中間欠損補綴用パツチ、腹部
の細胞組織補綴用パツチ、動、静脈血管補綴用パ
ツチ、心臓補綴用パツチ、心臓弁補綴物、心臓用
シート、ヘルニア補綴用パツチ、気管欠損補綴用
パツチなどの各種パツチ類を始め、人工血管や人
工皮膚または人工皮膚用シートなどがあるが、本
発明の有効性はこれによつて限定されたり、制限
を受けるものではなく、生体組織の欠損部を補綴
する部材または資材全てにわたるものである。 The bioprosthesis referred to in the present invention includes, for example, a patch for intermediate defect prosthesis in thoracic vascular surgery, a patch for abdominal cell tissue prosthesis, a patch for arterial and venous blood vessel prosthesis, a patch for cardiac prosthesis, a heart valve prosthesis, and a patch for prosthesis of abdominal tissue. There are various types of patches such as patches for hernia prosthesis, patches for prosthesis of tracheal defects, artificial blood vessels, artificial skin, and sheets for artificial skin, but the effectiveness of the present invention is limited by these, The term is not limited, and covers all members or materials for prosthetizing a defective part of living tissue.
本発明の最も特徴的な点は、まず第1に0.9デ
ニール以下の極細繊維により、芯糸と芯糸に対し
てスパイラル状に巻きつけたカバー糸から成るカ
バーリングヤーンが形成され、かつ織または編ま
たは組紐組織によつてシート状物やチユーブ状物
を始めとする種々の変形物を形成した点にある。
すなわち、極細繊維をカバーリングヤーンで構成
することにより、極めて単純な組織によつてシー
ト状物やチユーブ状物を始めとし、他の形成物を
形成しても、生体用補綴物の両面が実質的に極細
繊維によつて形成されるので該生体用補綴物の生
体適合性を極めて有効に高めることが出来るので
ある。しかも生体用補綴物の厚みを極めて薄く出
来得る点にある。 The most characteristic feature of the present invention is that firstly, a covering yarn consisting of a core yarn and a cover yarn spirally wound around the core yarn is formed using ultrafine fibers of 0.9 denier or less, and is woven or The point is that various deformed objects including sheet-like objects and tube-like objects are formed by knitting or braiding.
In other words, by composing microfibers with covering yarns, even if sheet-like objects, tube-like objects, or other structures are formed using extremely simple structures, both sides of the bioprosthesis will remain virtually intact. Since it is made of ultrafine fibers, the biocompatibility of the bioprosthesis can be extremely effectively improved. Moreover, the thickness of the bioprosthesis can be made extremely thin.
勿論、多層構造の少なくとも一部に該カバーリ
ングヤーンを適用することによつて、比較的厚み
を要求されるような生体用補綴物も随時提供し得
ることは言うまでもない。 Of course, by applying the covering yarn to at least a portion of the multilayer structure, it is possible to provide a bioprosthesis that requires a relatively large thickness.
その第2は、ほつれを止めるために行なう高圧
流体処理において、該高圧流体処理圧を低くし得
る点にあり、この低圧処理が出来たことで、ケバ
発生や強度劣化がなくなつた点である。この効果
は、本発明者の豊かな経験と知識をもつてして
も、思いもよらない効果であつた。その理由は定
かではないが、少なくとも極細繊維をカバーリン
グヤーンのカバー糸として使用していることに起
因しているものと考えられる。 The second reason is that the high-pressure fluid treatment pressure used to stop fraying can be lowered, and this low-pressure treatment eliminates the occurrence of fuzz and strength deterioration. . This effect was unexpected even with the rich experience and knowledge of the present inventor. The reason for this is not clear, but it is thought to be at least due to the fact that ultrafine fibers are used as the covering yarn of the covering yarn.
すなわち、本発明でいうカバーリングヤーンを
用いて織編組織または組紐組織によつてチユーブ
を形成した場合には、隣接するカバー糸からなる
繊維束は、外側に存在するお互いの極細繊維が直
接的に接触する形態を有しており、かつ並列的配
列ではなく互いに重なるがごとくかみ合い易い配
列を有する結果、比較的低圧での高圧流体処理に
よつて極細繊維のからまり合いが促進され、充分
な耐ほつれ性を付与できるようになつたものと思
われる。さらにこのからまり合い効果を高めるた
め芯糸に高収縮繊維を用いチユーブ形成後収縮さ
せると鞘部の極細繊維のスパイラルのピツチが縮
まり、繊維の実質的たるみが生じるため高圧流体
処理による著しいからまり合い効果が生じ、耐ほ
つれ性がより改善される。この場合、芯糸の収縮
は、10%以上のものが好ましい。更に好ましくは
15%以上である。 That is, when a tube is formed by a weaving or knitting structure or a braided structure using the covering yarn referred to in the present invention, the fiber bundles made of adjacent covering yarns are directly connected to each other's ultrafine fibers existing on the outside. As a result of having an arrangement in which the ultrafine fibers are in contact with each other and are arranged in such a manner that they are easily interlocked as if they overlap each other rather than in a parallel arrangement, the entanglement of the ultrafine fibers is promoted by high-pressure fluid treatment at a relatively low pressure, resulting in sufficient It seems that it has become possible to impart fraying resistance. Furthermore, in order to enhance this entanglement effect, if high shrinkage fibers are used as the core yarn and are shrunk after forming the tube, the pitch of the spiral of the ultrafine fibers in the sheath will shrink, resulting in substantial sagging of the fibers, resulting in significant tangles due to high-pressure fluid treatment. A mating effect occurs, and fraying resistance is further improved. In this case, the shrinkage of the core yarn is preferably 10% or more. More preferably
15% or more.
本発明でいうカバーリングヤーンは、例えばカ
バーリングマシン(例えば片岡機械工業(株)製、型
式SR)によつて形成することができる。芯糸と
カバー糸の単糸繊度は特にこだわらないが芯糸を
太く、カバー糸を細くする方が良い結果が得られ
る場合が多い。 The covering yarn referred to in the present invention can be formed, for example, by a covering machine (for example, model SR, manufactured by Kataoka Kikai Kogyo Co., Ltd.). Although the single yarn fineness of the core yarn and cover yarn is not particularly important, better results can often be obtained by making the core yarn thicker and the cover yarn thinner.
具体的には芯糸としては単糸繊度が0.5デニー
ル以上の繊維を用いるのが好ましく、より好まし
くは1.0デニール以上の繊維を用いるのが好まし
いが、0.5デニール以下でも好ましい場合がある。
例えば、極細繊維(A)に0.05デニール以下の繊維を
カバー糸として用いる場合には、芯糸は0.3デニ
ールぐらいのものを用いても好ましい場合があ
る。 Specifically, it is preferable to use fibers with a single filament fineness of 0.5 denier or more, more preferably 1.0 denier or more, but 0.5 denier or less may be preferable in some cases.
For example, when a fiber of 0.05 denier or less is used as the cover yarn for the ultrafine fiber (A), it may be preferable to use a core yarn of about 0.3 denier.
また、カバー糸は後述する極細繊維を用いるの
が最も好ましいが、使用目的と場合によつては芯
糸の繊維より太くても、良い結果を生じる。 Further, it is most preferable to use ultrafine fibers as described below for the cover yarn, but depending on the purpose of use and the case, good results can be obtained even if the cover yarn is thicker than the fiber of the core yarn.
すなわち、目的とする生体用補綴物やその形状
によつてはあえて芯糸に極細繊維とカバー糸に超
極細繊維を用いた方が好結果を得る場合もある。
また、カバーリングの形態はS撚りまたはZ撚り
の一方撚りであつても、SまたはZ撚りした後更
にZまたはS撚りを加えたような方法でも良く、
更にその上にカバー糸を交互に巻き加えられたよ
うな方法でも良い。 That is, depending on the intended bioprosthesis and its shape, better results may be obtained by intentionally using ultrafine fibers for the core yarn and ultrafine fibers for the cover yarn.
In addition, the form of the covering may be one of S twist or Z twist, or a method in which Z or S twist is added after S or Z twist,
Furthermore, a method in which cover threads are alternately wound on top of the threads may also be used.
本発明で、素材繊維として用いるポリマーは、
ポリエステル、ポリアミド、ポリテトラフルオル
エチレン、ポリオレフイン、コラーゲン繊維など
を言い、特に生体に対する特性がこれらのポリマ
ーと差異がなければ特にその種類は問わないが、
中でも特にポリエステルが好ましい。勿論、場合
によつては、2種以上のポリマーを用いても好結
果を得られる場合があり、さらに場合によつては
その方がより好ましい場合すらある。 In the present invention, the polymer used as the material fiber is
It refers to polyester, polyamide, polytetrafluoroethylene, polyolefin, collagen fiber, etc., and the type is not particularly important as long as its properties against living organisms are not different from these polymers.
Among these, polyester is particularly preferred. Of course, in some cases, good results may be obtained by using two or more types of polymers, and in some cases, this may even be more preferable.
また、本発明で用いる極細繊維は、繊維の単糸
繊度は0.9デニール以下好ましくは0.5デニール以
下の極細繊維を言い、更に特に好ましくは0.2デ
ニール以下の極細繊維を言う。 Further, the ultrafine fibers used in the present invention refer to ultrafine fibers whose single fiber fineness is 0.9 denier or less, preferably 0.5 denier or less, and more preferably 0.2 denier or less.
カバーリングヤーンの形成にあたつては、化学
的あるいは物理的手段によつて極細化可能な繊維
を用いてカバーリングヤーンを形成し、次いで極
細化しないチユーブを形成あるいは極細化した後
チユーブを形成し、極細化しないでチユーブを形
成した場合には次いで極細化することにより、結
果的に極細繊維をカバー糸としたカバーリングヤ
ーンでチユーブが形成されたようにしても良い。 In forming the covering yarn, a covering yarn is formed using fibers that can be made ultra-fine by chemical or physical means, and then a tube is formed that does not become ultra-fine, or a tube is formed after ultra-fine. However, in the case where the tube is formed without making it ultra-fine, it may be made ultra-fine next, so that the tube may be formed with a covering yarn using the ultra-fine fiber as the covering yarn.
また、すでにかかる極細繊維の形態となつてい
る繊維をそのまま用いてカバーリングヤーンを形
成しても良い。この場合は、その後の極細化処理
は省略されることはいうまでもない。 Alternatively, the covering yarn may be formed by using fibers that are already in the form of ultrafine fibers as they are. In this case, it goes without saying that the subsequent ultra-fine processing is omitted.
極細繊維を得る方法としては通常の紡糸方法で
十分の注意を払つて得ることができるが、ポリエ
ステルの場合のように末延伸糸を特定の条件下で
延伸し、極細繊維となすことも可能である。一
方、後手段により極細化可能な繊維としては多成
分系繊維の一成分を除去するか、もしくは剥離さ
せるか等の手段によりフイブリル化もしくは極細
化するタイプの繊維を意味する。 Ultra-fine fibers can be obtained by using normal spinning methods with due care, but it is also possible to create ultra-fine fibers by drawing the end-drawn yarn under specific conditions, as in the case of polyester. be. On the other hand, fibers that can be made ultrafine by post-processing means fibers that can be fibrillated or made ultrafine by removing or exfoliating one component of a multicomponent fiber.
また、多成分繊維を用いる場合は最終的に残る
ポリマーは前記ポリマーであるが他の組み合せ成
分としてはポリスチレン、ポリエチレン、水溶性
ポリアミド、アルカリ水溶液可溶型ポリエステ
ル、熱水可溶型ポリエステル、水溶性ポリビニル
アルコール等を適宜組合せることが可能である。
かかるポリマーの組合せは製糸性、加工性、機能
性や不純物、残存物の除去性等を見て場合に応じ
て決定されるものである。 In addition, when using multi-component fibers, the final polymer remaining is the above-mentioned polymer, but other combined components include polystyrene, polyethylene, water-soluble polyamide, alkaline aqueous solution-soluble polyester, hot water-soluble polyester, and water-soluble polyester. It is possible to appropriately combine polyvinyl alcohol and the like.
The combination of such polymers is determined depending on the case, taking into consideration thread-spinning properties, processability, functionality, removability of impurities and residues, etc.
また、極細繊維間および/または太繊度繊維の
繊維間の間隙を有する形態と成すには、海島型の
高分子配列体繊維を用いる方がより好ましい。ま
た多成分ブレンド型の繊維も考えられるが繊維の
脱落が若干懸念される。しかし、その点以外は同
様の効果も得られる。すなわち該間隙を有する形
態と成すことにより、柔軟性や高圧液流処理によ
つて付与される絡合によつて耐ほつれ性を更に効
果的ならしめる。 Further, in order to form a structure having gaps between ultrafine fibers and/or between thick fibers, it is more preferable to use sea-island type polymer array fibers. Multi-component blend type fibers are also considered, but there is some concern that the fibers may fall off. However, similar effects can be obtained in other respects. That is, by forming the material with the gap, the fraying resistance is made more effective due to the flexibility and the entanglement imparted by the high-pressure liquid flow treatment.
また、後手段による極細化可能な繊維の場合、
カバーリングヤーンの形成や、チユーブ加工時は
通常の繊維の太さであつても加工後極細化できる
ため加工上のトラブル例えば製織や製編や製紐
時、製織や製編やコアヤーン形成前やカバー糸の
各種の糸加工手段を講じる場合の糸切れや毛羽発
生等を最少限に抑えることができて好ましい。又
高圧液流体処理の効果を高めるために製織、製編
後に起毛処理、例えば起毛機による方法やシヤー
リング機による方法、場合によつてはサンドペー
パーでこする方法などによつて、高圧流で噴射処
理する前に毛羽及び/又はループを形成した方が
良い場合もある。 In addition, in the case of fibers that can be made ultra-fine by post-processing,
During the formation of covering yarn and tube processing, even if the fiber is of normal thickness, it can be made extremely fine after processing, so there are problems during processing, such as during weaving, knitting, stringing, before weaving, knitting, or core yarn formation. This is preferable because yarn breakage, fuzz generation, etc. can be minimized when various yarn processing methods are applied to the cover yarn. In addition, in order to enhance the effect of high-pressure liquid fluid treatment, high-pressure jets are applied after weaving or knitting, such as by using a raising machine, by using a shearing machine, or in some cases by rubbing with sandpaper. In some cases, it may be advantageous to form fluff and/or loops before processing.
またカバー糸は微細ケン縮を有するような繊維
を用いるのも好ましい結果を得る。 Preferable results can also be obtained by using fibers with fine crimp as the cover yarn.
高圧流による交絡処理の方法は種々考えられる
が液体による方法がより効率的であり、中でもウ
オータージエツト流による方法が安全性及び経済
性の点から最も好ましい。 Although various methods for the entanglement treatment using high-pressure flow can be considered, a method using a liquid is more efficient, and among them, a method using a water jet flow is the most preferable from the viewpoints of safety and economy.
また、噴射圧は小さ過ぎると絡まないが、大き
過ぎると繊維が切断してしまつて良くない。この
範囲の中で繊維の強度やその時の繊度や束の太
さ、また生体用補綴物の柔軟性などによつて適宜
決められる。 Also, if the spray pressure is too low, the fibers will not get tangled, but if the spray pressure is too high, the fibers will be cut, which is not good. Within this range, it can be appropriately determined depending on the strength of the fiber, the fineness and thickness of the bundle, the flexibility of the bioprosthesis, etc.
またウオータージエツトパンチは基本組織の周
期と一致しないように、左右に揺動させたり、サ
イクリツクに揺動させることが好ましい。これに
より、パンチ筋やモワレ現象を軽減させることが
できるばかりでなく、もれなく全体にしかもすみ
ずみまで交絡せしめることが出来る。 Further, it is preferable that the waterjet punch be oscillated from side to side or cyclically so as not to match the period of the basic tissue. This not only makes it possible to reduce punch streaks and moiré phenomena, but also makes it possible to intertwine the entire fabric and even every nook and cranny.
更にシート状物やチユーブ状物を裏返して高圧
流処理を行なうならば、より耐ほつれ性を向上し
得るが、必ずしも必須ではない。 Furthermore, if the sheet-like material or tube-like material is turned over and subjected to high-pressure flow treatment, the fraying resistance can be further improved, but this is not always necessary.
また人工血管の製法の場合には、布帛をチユー
ブ化する必要があるが、このチユーブ化の手段と
しては、布帛と成した後裁断し、縫製や接着や融
着などの手段によつてチユーブ状物と成すことも
できるが、基本組織を形成するに際し、チユーブ
状に形成した方が継ぎ目がなくなり好ましい。 In addition, in the case of the manufacturing method of artificial blood vessels, it is necessary to form the fabric into tubes, and the method for forming the tubes is to cut the fabric after it is made into a fabric, and then to make the tube shape by sewing, gluing, fusing, etc. Although it can be formed into a solid object, it is preferable to form the basic structure into a tube shape, since this eliminates seams.
一方、シート状物やチユーブ状物などを形成す
る場合、前記カバーリングヤーンだけで形成して
も良いが、目的とする生体用補綴物によつては、
前記カバーリングヤーンと他の極細繊維および/
または太繊度繊維などとの組合せによつてチユー
ブを形成するのも好ましく、またその方がより良
い効果を生む場合もある。 On the other hand, when forming a sheet-like object or a tube-like object, it may be formed using only the covering yarn, but depending on the intended bioprosthesis,
The covering yarn and other microfibers and/or
Alternatively, it is also preferable to form a tube in combination with a thick fiber or the like, and this may produce better effects.
次に実施例によつて本発明をより判り易く説明
するが、本発明の有効性や権利の範囲はこれによ
つて限定されたり制限を受けるものではない。
Next, the present invention will be explained more clearly with reference to Examples, but the validity and scope of rights of the present invention are not limited or restricted thereby.
実施例 1
芯糸にポリエチレンテレフタレート50デニール
24フイラメント、カバー糸に島成分がポリエチレ
ンテレフタレート50部、海成分がポリスチレン50
部、島数16島の繊度75デニール18フイラメントの
を用い、カバーリングマシン(片岡機械工業(株)
製・型式SR)によつて、カバーリングヤーンを
形成した。条件は、糸速5.3m/分、カバー糸の
スピンドル回転数8000T/分、S方向、Z方向と
もにカバーリングを行なつた。Example 1 Polyethylene terephthalate 50 denier core yarn
24 filament, cover yarn has an island component of 50 parts polyethylene terephthalate, and a sea component of 50 parts polystyrene.
Covering machine (Kataoka Machine Industry Co., Ltd.) using 75 denier 18 filament with 16 islands.
A covering yarn was formed using the following method: The conditions were a yarn speed of 5.3 m/min, a cover yarn spindle rotation speed of 8000 T/min, and covering was performed in both the S direction and the Z direction.
次いで、得られたカバーリングヤーンを糊付、
整経し、細巾ネーム織機を用いて平織組織による
チユーブを形成した。またヨコ糸にも該カバーリ
ングヤーンを用いた。チユーブは織上りの内径13
mmφ、長さ100cm、織上り密度タテ×ヨコ=17
本/cm×15本/cmであつた。 Then, the resulting covering yarn is glued,
It was warped and a plain weave tube was formed using a narrow cloth name loom. The covering yarn was also used for the weft yarn. The tube has a woven inner diameter of 13
mmφ, length 100cm, weaving density vertical x horizontal = 17
It was 15 books/cm x 15 books/cm.
次いでこのチユーブを湯洗し、乾燥し、トリク
ロルエチレンでポリスチレンを除去して極細化し
た。 Next, this tube was washed with hot water, dried, and the polystyrene was removed with trichlorethylene to make it ultra-fine.
得られた人工血管は、内外壁とも極細繊維によ
つて覆われ、しかもしなやかで非常になめらかな
タツチものであつた。さらに詳しく見ると芯糸に
用いた太繊度がところどころに見えていたが、実
質的には極細繊維が覆つていた。更に針通過性を
調べたところとてもスムースに運針できた。この
チユーブに吐出孔0.25mmφ、吐出孔間隔2.5mm、
圧力20Kg/cm2の条件でウオータージエツトパンチ
処理を行なつた。 The obtained artificial blood vessel had both inner and outer walls covered with ultrafine fibers, and had a supple and extremely smooth texture. Looking more closely, the thick fibers used for the core yarn were visible here and there, but were essentially covered by ultra-fine fibers. Furthermore, when I checked the needle passage performance, I found that the needle moved very smoothly. This tube has a discharge hole of 0.25mmφ, a discharge hole interval of 2.5mm,
Waterjet punching was carried out at a pressure of 20 kg/cm 2 .
得られた人工血管は、「耐ほつれ性」がウオー
タージエツト処理をしないものに比べはるかに優
れ、しかもしなやかであつた。しかし、更に「耐
ほつれ性」を付与するため、同一条件で圧力のみ
40Kg/cm2としてウオータージエツトパンチ処理を
行なつたところ、更に「耐ほつれ性」が改善され
た。 The resulting artificial blood vessel had far superior "fray resistance" compared to those not treated with waterjet, and was more flexible. However, in order to further impart "fray resistance", only pressure is applied under the same conditions.
When water jet punching was carried out at 40 kg/cm 2 , the "fray resistance" was further improved.
しかも人工血管の内外壁は極細繊維で覆われ、
とてもタツチの良いものであつた。該人工血管を
更に詳細に顕微鏡で観察したところ、極細繊維が
単糸繊維間や織り目間また繊維束間に互いに多数
重なり合うように交絡しているのが観察できた。
さらに詳細に調べると太い繊維の一部がところど
ころに見えていたが、主として、極細繊維が人工
血管壁の両面に存在していた。また、ウオーター
ジエツトパンチ処理をした面の反対側の面には、
短い毛羽が若干存在していた。 Moreover, the inner and outer walls of the artificial blood vessel are covered with ultrafine fibers,
It was very touchy. When the artificial blood vessel was observed in more detail under a microscope, it was observed that the ultrafine fibers were intertwined so as to overlap each other in large numbers between single fibers, between textures, and between fiber bundles.
Upon closer examination, some thick fibers were visible here and there, but mainly ultrafine fibers were present on both sides of the artificial blood vessel wall. Also, on the side opposite to the waterjet punched side,
Some short fuzz was present.
実施例 2
実施例1の海成分をテレフタル酸、イソフタル
酸、ソデイウムスルホンイソフタル酸とエチレン
グリコールからの熱水可溶ポリマとして、脱海成
分を熱水に変えた以外は実施例1と全く同様にし
て同様の結果を得た。Example 2 Completely the same as Example 1 except that the sea component in Example 1 was changed to a hot water soluble polymer made from terephthalic acid, isophthalic acid, sodium sulfone isophthalic acid, and ethylene glycol, and the sea removal component was changed to hot water. Similar results were obtained in the same manner.
本発明の効果を列挙すると次のようになる。 The effects of the present invention are enumerated as follows.
(1) 生体適合性に優れた極細繊維を、カバーリン
グヤーンとして用いているので生体用補綴物の
両面に配することが出来、微細な繊維間隙への
フイブリル沈着に優れている。(1) Ultrafine fibers with excellent biocompatibility are used as covering yarns, so they can be placed on both sides of a bioprosthesis, and have excellent fibril deposition in the fine fiber gaps.
(2) 単純な織編組織または組紐組織で充分な性能
を達成することが出来るので、生体用補綴物の
厚みを極めて薄くでき、医療部材または資材と
しての帆用性に優れる。(2) Since sufficient performance can be achieved with a simple woven or braided structure, the thickness of the bioprosthesis can be made extremely thin, and it has excellent usability as a medical component or material.
(3) 極細繊維のカバーリングヤーンを用いている
ので高圧流体処理を低圧でも優れた交絡性を有
し、しかも起毛処理をしなくても、ほつれなく
出来るので、抜け毛や繊維くずの脱落や繊維強
度の低下がない。(3) Because it uses ultra-fine fiber covering yarn, it has excellent entangling properties even when treated with high-pressure fluid at low pressure.Furthermore, it can be done without fraying without needing a napping treatment, so it prevents hair loss and fiber waste from falling off and fibers. There is no decrease in strength.
Claims (1)
ングヤーンで構成された生体用補綴物であつて、
該生体用補綴物を構成する極細繊維の少なくとも
一部が該ヤーン間で交絡していることを特徴とす
る生体用補綴物。 2 生体用補綴物を製造するに際し、少なくとも
下記〜の工程を含みかつ順に行なうことを特
徴とする生体用補綴物の製法。 カバーリングヤーンを形成する工程。 該カバーリングヤーンを用いた織、編組織ま
たは組紐組織によつて、シート状物またはチユ
ーブ状物を形成する工程。 該シート状物またはチユーブ状物に高圧流体
処理を施す工程。 3 カバーリングヤーンの芯糸が沸湯水中収縮率
10%以上を有する高収縮繊維である特許請求の範
囲第2項に記載の生体用補綴物の製法。[Scope of Claims] 1. A bioprosthesis composed of a covering yarn containing ultrafine fibers of 0.9 denier or less,
A bioprosthesis characterized in that at least a portion of the ultrafine fibers constituting the bioprosthesis are intertwined between the yarns. 2. A method for manufacturing a bioprosthesis, which includes at least the following steps and is performed in order. Process of forming covering yarn. A step of forming a sheet-like object or a tube-like object by weaving, knitting or braiding the covering yarn. A step of subjecting the sheet-like material or tube-like material to high-pressure fluid treatment. 3. Shrinkage rate of core thread of covering yarn in boiling water
The method for producing a bioprosthesis according to claim 2, wherein the bioprosthesis is made of high shrinkage fibers having a content of 10% or more.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP61174526A JPS6331668A (en) | 1986-07-24 | 1986-07-24 | Prosthesis for living body and its production |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP61174526A JPS6331668A (en) | 1986-07-24 | 1986-07-24 | Prosthesis for living body and its production |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS6331668A JPS6331668A (en) | 1988-02-10 |
JPH0369543B2 true JPH0369543B2 (en) | 1991-11-01 |
Family
ID=15980064
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP61174526A Granted JPS6331668A (en) | 1986-07-24 | 1986-07-24 | Prosthesis for living body and its production |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS6331668A (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2090624A1 (en) | 2008-02-13 | 2009-08-19 | FUJIFILM Corporation | Ink set for inkjet recording and image recording method |
EP2166046A1 (en) | 2008-09-19 | 2010-03-24 | FUJIFILM Corporation | Ink set and inkjet recording method |
US8393725B2 (en) | 2009-08-28 | 2013-03-12 | Fujifilm Corporation | Ink set and image forming method |
Families Citing this family (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2002330481A (en) * | 2001-04-27 | 2002-11-15 | Matsushita Electric Ind Co Ltd | Interlocking function device with external device |
JP4627978B2 (en) * | 2003-10-27 | 2011-02-09 | 泰晴 野一色 | Low blood permeability medical material |
US9243353B2 (en) | 2011-01-26 | 2016-01-26 | Asahi Kasei Fibers Corp. | Stent grafts |
-
1986
- 1986-07-24 JP JP61174526A patent/JPS6331668A/en active Granted
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2090624A1 (en) | 2008-02-13 | 2009-08-19 | FUJIFILM Corporation | Ink set for inkjet recording and image recording method |
EP2166046A1 (en) | 2008-09-19 | 2010-03-24 | FUJIFILM Corporation | Ink set and inkjet recording method |
US8393725B2 (en) | 2009-08-28 | 2013-03-12 | Fujifilm Corporation | Ink set and image forming method |
Also Published As
Publication number | Publication date |
---|---|
JPS6331668A (en) | 1988-02-10 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP0179600B1 (en) | Artificial blood vessel and method of manufacture | |
CN108472122B (en) | Medical fabric | |
CN111417362A (en) | Medical fabric | |
EP0128741B1 (en) | Artificial vascular graft | |
CN111295154A (en) | Medical fabric | |
JPS59218158A (en) | Blood vessel implant piece having cross structure | |
JPS6158190B2 (en) | ||
JPH0369543B2 (en) | ||
JPH11164881A (en) | Medical material and manufacture thereof | |
JP2005187994A (en) | Elasticized toweling | |
JPH01126962A (en) | Preparation of medical prosthesis | |
JPH0340845A (en) | Wind-protecting knit fabric and production thereof | |
WO2021117894A1 (en) | Woven fabric to be used in medical device for chest disease, and medical device for chest disease | |
JPH0528143B2 (en) | ||
JP7341416B2 (en) | medical gauze | |
JP6638437B2 (en) | Mixed yarn, woven or knitted fabric using the same, and suede-like woven or knitted fabric | |
JPH0462741B2 (en) | ||
JP2016180189A (en) | Commingled yarn, suede tone woven or knitted fabric and method for producing suede tone woven or knitted fabric | |
JP3418953B2 (en) | Fiber structure | |
JPH07119028A (en) | Antipilling spun web | |
JPH09228167A (en) | Polyester blended yarn and its production | |
JPH067387A (en) | Artificial blood vessel and its production | |
JP2001040545A (en) | Production of cloth having excellent bulkiness and soft feeling | |
JPH03260167A (en) | Production of peach-like knitted fabric | |
JPH01246468A (en) | Production of high-density cloth |