JPH0588611B2 - - Google Patents
Info
- Publication number
- JPH0588611B2 JPH0588611B2 JP61260719A JP26071986A JPH0588611B2 JP H0588611 B2 JPH0588611 B2 JP H0588611B2 JP 61260719 A JP61260719 A JP 61260719A JP 26071986 A JP26071986 A JP 26071986A JP H0588611 B2 JPH0588611 B2 JP H0588611B2
- Authority
- JP
- Japan
- Prior art keywords
- fibers
- artificial blood
- blood vessel
- ultrafine fibers
- fine
- 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
- 229920001410 Microfiber Polymers 0.000 claims description 37
- 210000004204 blood vessel Anatomy 0.000 claims description 30
- 239000002473 artificial blood Substances 0.000 claims description 29
- 239000000835 fiber Substances 0.000 claims description 25
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 23
- 230000035699 permeability Effects 0.000 claims description 19
- 230000035602 clotting Effects 0.000 claims description 13
- 238000009940 knitting Methods 0.000 claims description 11
- 238000009941 weaving Methods 0.000 claims description 11
- 238000009954 braiding Methods 0.000 claims description 9
- 238000000034 method Methods 0.000 description 12
- 210000004369 blood Anatomy 0.000 description 10
- 239000008280 blood Substances 0.000 description 10
- 230000015572 biosynthetic process Effects 0.000 description 7
- 230000000694 effects Effects 0.000 description 7
- -1 polytetrafluoroethylene Polymers 0.000 description 7
- 239000000463 material Substances 0.000 description 6
- 210000001519 tissue Anatomy 0.000 description 6
- 206010053567 Coagulopathies Diseases 0.000 description 5
- 229920000139 polyethylene terephthalate Polymers 0.000 description 5
- 239000005020 polyethylene terephthalate Substances 0.000 description 5
- 229920000642 polymer Polymers 0.000 description 5
- 241000282472 Canis lupus familiaris Species 0.000 description 4
- 230000035876 healing Effects 0.000 description 4
- 102000008186 Collagen Human genes 0.000 description 3
- 108010035532 Collagen Proteins 0.000 description 3
- 229920000297 Rayon Polymers 0.000 description 3
- HEMHJVSKTPXQMS-UHFFFAOYSA-M Sodium hydroxide Chemical compound [OH-].[Na+] HEMHJVSKTPXQMS-UHFFFAOYSA-M 0.000 description 3
- YXFVVABEGXRONW-UHFFFAOYSA-N Toluene Chemical compound CC1=CC=CC=C1 YXFVVABEGXRONW-UHFFFAOYSA-N 0.000 description 3
- 229920001436 collagen Polymers 0.000 description 3
- 210000004954 endothelial membrane Anatomy 0.000 description 3
- 238000002513 implantation Methods 0.000 description 3
- 229920000728 polyester Polymers 0.000 description 3
- 239000002964 rayon Substances 0.000 description 3
- 230000023555 blood coagulation Effects 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 229920001343 polytetrafluoroethylene Polymers 0.000 description 2
- 239000004810 polytetrafluoroethylene Substances 0.000 description 2
- 230000002265 prevention Effects 0.000 description 2
- 229910001220 stainless steel Inorganic materials 0.000 description 2
- 239000010935 stainless steel Substances 0.000 description 2
- 239000000126 substance Substances 0.000 description 2
- 241000239290 Araneae Species 0.000 description 1
- 229920001634 Copolyester Polymers 0.000 description 1
- 102000009123 Fibrin Human genes 0.000 description 1
- 108010073385 Fibrin Proteins 0.000 description 1
- BWGVNKXGVNDBDI-UHFFFAOYSA-N Fibrin monomer Chemical compound CNC(=O)CNC(=O)CN BWGVNKXGVNDBDI-UHFFFAOYSA-N 0.000 description 1
- YCKRFDGAMUMZLT-UHFFFAOYSA-N Fluorine atom Chemical compound [F] YCKRFDGAMUMZLT-UHFFFAOYSA-N 0.000 description 1
- 241000157049 Microtus richardsoni Species 0.000 description 1
- 229930182556 Polyacetal Natural products 0.000 description 1
- 239000004952 Polyamide Substances 0.000 description 1
- 239000004793 Polystyrene Substances 0.000 description 1
- 240000005578 Rivina humilis Species 0.000 description 1
- 230000002745 absorbent Effects 0.000 description 1
- 239000002250 absorbent Substances 0.000 description 1
- 230000003872 anastomosis Effects 0.000 description 1
- 239000011324 bead Substances 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 230000000052 comparative effect Effects 0.000 description 1
- 239000002131 composite material Substances 0.000 description 1
- 230000001010 compromised effect Effects 0.000 description 1
- 229950003499 fibrin Drugs 0.000 description 1
- 239000012530 fluid Substances 0.000 description 1
- 229910052731 fluorine Inorganic materials 0.000 description 1
- 239000011737 fluorine Substances 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 210000004379 membrane Anatomy 0.000 description 1
- 239000012528 membrane Substances 0.000 description 1
- 239000003658 microfiber Substances 0.000 description 1
- 239000002245 particle Substances 0.000 description 1
- 229920002647 polyamide Polymers 0.000 description 1
- 229920002959 polymer blend Polymers 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 229920006324 polyoxymethylene Polymers 0.000 description 1
- 229920001296 polysiloxane Polymers 0.000 description 1
- 229920002223 polystyrene Polymers 0.000 description 1
- 229920002635 polyurethane Polymers 0.000 description 1
- 239000004814 polyurethane Substances 0.000 description 1
- 239000011148 porous material Substances 0.000 description 1
- 238000002203 pretreatment Methods 0.000 description 1
- 230000002787 reinforcement Effects 0.000 description 1
- 229920002379 silicone rubber Polymers 0.000 description 1
- 239000004945 silicone rubber Substances 0.000 description 1
- 235000011121 sodium hydroxide Nutrition 0.000 description 1
- 230000002537 thrombolytic effect Effects 0.000 description 1
- 230000001732 thrombotic effect Effects 0.000 description 1
- 239000002759 woven fabric Substances 0.000 description 1
Landscapes
- Prostheses (AREA)
Description
【発明の詳細な説明】
［産業上の利用分野］
本発明は、極めて優れた生体適合性と実際の体
内への植え込むに当たり、その前処理として行わ
れるプリクロツテイング性に優れた人工血管に関
するものである。[Detailed Description of the Invention] [Field of Industrial Application] The present invention relates to an artificial blood vessel that has extremely excellent biocompatibility and excellent pre-clotting properties as a pretreatment for actual implantation into the body. It is.
［従来の技術］
内面に生体の内皮膜を形成するタイプの人工血
管では、治癒効果を高めるためにはなるべく生体
外の異物が少ないハイポロシテイ構造の人工血管
とする必要があるが、ハイポロシテイにすると、
血液の漏れが生じて実用に供し得ないか、もしく
は用途が著しく制限される。また、特に極細繊維
を用いることにより多少のプリクロツテイング性
を改善できるとの知見もあるが、単なる極細繊維
を用いるだけで十分なプリクロツテイング性を付
与することはできない。従来ではこのためやむを
えず治癒効果は多少犠牲にし、血漏が妨げる程度
までにローポロシテイ化して妥協した状態のもの
を利用していた。[Prior Art] In order to enhance the healing effect of a type of artificial blood vessel that forms an endothelial membrane of a living body on its inner surface, it is necessary to have a high-porosity structure with as few foreign substances as possible outside the body.
Blood leakage occurs, making it impossible to put it to practical use or severely limiting its use. In addition, there is knowledge that the preclotting property can be improved to some extent by particularly using ultrafine fibers, but sufficient preclotting properties cannot be imparted simply by using ultrafine fibers. Conventionally, for this reason, the healing effect was unavoidably sacrificed to some extent, and a compromised state was used in which the porosity was reduced to the extent that blood leakage was hindered.
［発明が解決しようとする課題］
本発明の目的は、治癒効果（生体適合性）と欠
漏防止を同時に満足する画期的な人工血管を提供
せんとするものである。[Problems to be Solved by the Invention] An object of the present invention is to provide an innovative artificial blood vessel that simultaneously satisfies a healing effect (biocompatibility) and prevention of leakage.
［課題を解決するための手段］ 本発明は、次の手段により達成される。[Means to solve the problem] The present invention is achieved by the following means.
(1)織り、編み、あるいは組紐等の基本構造を有
し、透水率が600ml／min・cm2・120mmHg以上
の人工血管において、該基本構造の組織目の空
間部に、1dtex以下の極細繊維が薄く存在した
状態を有してなることを特徴とする生体適合性
とプリクロツテイング性に優れた人工血管。(1) In an artificial blood vessel that has a basic structure such as weaving, knitting, or braiding, and has a water permeability of 600 ml/min・cm 2・120 mmHg or more, ultrafine fibers of 1 dtex or less are placed in the interstitial spaces of the basic structure. An artificial blood vessel having excellent biocompatibility and pre-clotting properties, characterized in that it has a thin state of being present.
(2) 織り、編み、あるいは組紐等の基本構造を有
し、透水率が600ml／min・cm2・120mmHg以上
の人工血管において、該人工血管が極細繊維を
含む多重組織からなり、少なくとも細繊度の目
の細かい層とそれよりも太繊度で目の粗い層と
から構成されてなるとともに、前記太繊度の基
本構造の組繊目の空間部には、1dtex以下の極
細繊維が薄く存在した状態を有してなることを
特徴とする生体適合性とプリクロツテイング性
に優れた人工血管。(2) Artificial blood vessels that have a basic structure such as weaving, knitting, or braiding, and have a water permeability of 600 ml/min・cm 2・120 mmHg or more, where the artificial blood vessels are composed of multiple tissues containing ultrafine fibers and have at least a fineness. It is composed of a fine-grained layer and a thicker and coarser layer, and a thin layer of ultrafine fibers of 1 dtex or less are present in the spaces between the interwoven fibers of the basic structure of the thicker fineness. An artificial blood vessel having excellent biocompatibility and pre-clotting properties.
［作用］ 以下、本発明を詳細に説明する。[Effect] The present invention will be explained in detail below.
本発明は比較的目の粗い織り、編み、組紐等の
基本構造を有し、かかる粗い織目、編目等の空隙
に細繊度（細番手）の極細繊維が散在するような
構造となさしめることである。従来の手段により
高透水率となるには例えば織組織の場合は目を粗
くせざるを得ない。このため、実際に生体内に植
え込むに当たつてはプリクロツテイングの前処理
が必要となる。しかし、このように単に目が粗い
だけの場合は十分なプリクロツテイング性が得ら
れないばかりか、プリクロツテイングが不十分な
状態で生体内に植え込んでも生体のわずかな血栓
溶解作用で容易に壁面からの血漏が生じ重大な問
題となる。しかし、本発明のごとく細繊度（細番
手）の極細繊維もしくは独立に分繊した極細繊維
が織り目または編目の間隙の空間部に縦横に僅か
でも存在する構造、より具体的には織り、編み、
組紐等の組織の目の空隙部に少なくとも１本以
上、好ましくは複数本の極細繊維が単独もしくは
集団として透水を妨げない程度い散在する構造で
あり、より理想的には独立した極細繊維が蜘蛛の
巣状にランダムに交錯して散在する構造となすこ
とにより、それが血液凝固のための核となり良好
なプリクロツテイングが可能となるのである。し
かも、極細繊維は細く広がつた状態で僅か存在す
るだけで十分であり、質量としては極めて少なく
て済み、このため、実質的に生体細胞形成のため
に好ましいとされている高透水構造の阻害要因と
はならない。この現象は極細繊維で構成されてい
るため、目ではほとんど感知できないような蜘蛛
の巣が、空気は良く通すが露は捕捉し大きな露の
玉ができる現象に似ている。すなわち血液が対象
となる人工血管では、本発明の構造とすることに
より一般の意味での透水性は十分有するものの、
組織の目の間の細番手もしくは薄く広がつた極細
繊維が血液の凝固核として作用しプリクロツテイ
ング性が著しく高められるのである。 The present invention has a basic structure such as relatively coarse weave, knitting, braiding, etc., and has a structure in which ultrafine fibers of fine fineness (fine count) are scattered in the voids of such coarse weave, knitting, etc. It is. In order to achieve high water permeability using conventional means, for example, in the case of a woven structure, the mesh must be made coarser. For this reason, pre-treatment of preclotting is required when actually implanting in a living body. However, if the openings are simply coarse, not only will sufficient preclotting properties not be obtained, but even if the implant is implanted in a living body with insufficient preclotting, it will be easily removed by the slight thrombolytic action of the living body. Blood leaks from the wall and becomes a serious problem. However, as in the present invention, a structure in which ultrafine fibers with fine fineness (fine count) or ultrafine fibers separated independently are present even slightly in the vertical and horizontal directions in the spaces between the weaves or the gaps between the stitches, more specifically weaving, knitting,
It is a structure in which at least one or more, preferably a plurality of ultrafine fibers are scattered individually or in groups to the extent that they do not impede water permeation in the gaps of a tissue such as a braid. By creating a structure in which the particles are randomly interlaced and scattered in a nest-like manner, they serve as nuclei for blood coagulation, allowing for good pre-clotting. Furthermore, it is sufficient to have only a small amount of ultrafine fibers in a thin and spread state, and their mass is extremely small. Therefore, they substantially inhibit the highly water-permeable structure that is considered preferable for the formation of living cells. Not a factor. This phenomenon is similar to the phenomenon in which spider webs, which are almost invisible to the eye because they are made of ultra-fine fibers, allow air to pass through but trap dew, creating large dew beads. In other words, although the structure of the present invention provides sufficient water permeability in the general sense of artificial blood vessels that handle blood,
The fine fibers between the eyes of the tissue or thinly spread ultrafine fibers act as blood coagulation nuclei, and the pre-clotting properties are significantly enhanced.
第１図、第２図に本発明を理解するための一助
としてその概念図による本発明による人工血管の
構造の１例を示した。 As an aid to understanding the present invention, FIGS. 1 and 2 show an example of the structure of an artificial blood vessel according to the present invention in a conceptual diagram.
第１図は、太番手よりなる目の粗い織物（組
織）１の空間部に極細繊維２が薄く分繊して散在
し、実質的に透水率を低下させずにプリクロツテ
イング性を上げられるような構造となつているも
のである。第２図は、特に多重組織で本発明にか
かる人工血管を構成した場合における人工血管構
造の１態様例を示したものであり、極細繊維より
なる細番手の目の細かい内面のチユーブ４の外側
に太番手の目の粗いチユーブ３が形成された２重
構造となつており、目の粗いチユーブ３の組織の
空間部にチユーブ４の細番手の極細繊維が存在す
るため、上記目的を達成できる状態となつてい
る。この構造は内、外逆転させてもよいことはい
うまでもない。かかる構造となすに当たつては、
織り、編み、あるいは組紐等の組織によつて作製
したチユーブに極細繊維となるべき真綿状のウエ
ツブを重ね、高速流体、例えば、ウオータージエ
ツト、エアージエツト等で処理する手段、織り、
編み、組紐等の組織を構成する繊維に1dtex以下
となるべき繊維で多くの弛みを有するヤーンを用
いてチユーブを形成する手段、1dtex以下の細繊
度細番手のヤーンを目の細かい組織としてそれよ
りも太番手のヤーンを粗い組織とした２重組織と
してチユーブを形成するか、一方の繊維で構成さ
れたチユーブに他方の繊維を巻きつける手段、も
しくは細番手、太番手で独立したチユーブを形成
しておき一方に他方を被せて一体化する手段など
がある。ここで細番手とは相対的意味であつて、
例えば目の粗い組織に用いる太番手に対し、それ
よりも相対的に細いことを意味する。しかし、一
般的意味で言う細番手の好ましい例は75Dtex以
下、好ましくは50Dtex以下より好ましくは
30Dtex以下であろう。これと組み合わせて用い
られる太番手のヤーンは当然これよりも太いもの
を用いることとなる。本発明では太番手ものでよ
り目の粗いチユーブ構造を形成し、これにより実
質的に高透水性の生体適合効果を発揮せしめる。
この生体適合効果を更に高めるためには1dtex以
下の極細繊維を細番手ヤーンに用いるのは当然と
して、この極細繊維を太番手ヤーンにも用いるこ
とができる。また、多重組織とは、一般的な意味
での２重、３重、……の構造をした織、編組織構
造や、あるいは、一重組織のものを重ね合わせた
構造を意味するものである。 Figure 1 shows that ultrafine fibers 2 are thinly separated and scattered in the spaces of a coarse woven fabric (structure) 1 made of thick yarn, which improves preclotting properties without substantially reducing water permeability. It has a structure like this. FIG. 2 shows an example of an embodiment of the artificial blood vessel structure in the case where the artificial blood vessel according to the present invention is constructed with multiple tissues. It has a double structure in which thick coarse tubes 3 are formed, and the ultrafine fibers of fine tubes 4 exist in the space of the structure of the coarse tubes 3, so that the above purpose can be achieved. It has become a state. It goes without saying that this structure may be reversed inside and out. In constructing such a structure,
Weaving, weaving, a method of layering a cotton-like web to become ultra-fine fibers on a tube made of a structure such as weaving, knitting, or braiding, and treating it with a high-speed fluid such as water jet, air jet, etc.
A means of forming a tube using a yarn with a lot of slack in the fibers constituting the structure of knitting, braiding, etc., which should be less than 1 dtex, and a method of forming a tube using yarn with a fineness and fine count of less than 1 dtex as a finer structure. Either the tube is formed as a double structure made of thick yarn with a coarse structure, or the tube made of one fiber is wound around the other fiber, or an independent tube is formed with fine yarn and thick yarn. There is a method of putting one over the other and integrating them. Here, fine count is a relative meaning,
For example, it means that it is relatively thinner than the thick one used for coarse texture. However, in a general sense, a preferable example of a fine count is 75Dtex or less, preferably 50Dtex or less, and more preferably 50Dtex or less.
Probably less than 30Dtex. Naturally, the thick yarn used in combination with this is thicker than this. In the present invention, a thick tube is used to form a coarser tube structure, thereby achieving a biocompatible effect of substantially high water permeability.
In order to further enhance this biocompatibility effect, it is natural to use ultrafine fibers of 1 dtex or less for fine count yarns, but these ultrafine fibers can also be used for thick yarns. Furthermore, the term "multiple weave" refers to a woven or knitted weave structure having a double, triple, etc. structure in a general sense, or a structure in which single weave structures are overlapped.
本発明では透水率として120mmHgの水圧下で１
cm2当たり１分間の透水量て定義される値が、600
ml／min・cm2・120mmHg以上さらに好ましくは
1200ml／min・cm2・120mmHg以上の透水率の高い
場合において極細繊維によるプリクロツテイング
性の効果が特に発揮される。また、このプリクロ
ツテイング性は細口径の人工血管の場合により重
要となり、６mmφ以下の場合にその効果が特に発
揮される。 In the present invention, the water permeability is 1 under a water pressure of 120 mmHg.
The value defined as water permeability per minute per cm2 is 600
ml/min・cm 2・120mmHg or more, more preferably
When the water permeability is high (1200ml/min・cm 2・120mmHg or more), the effect of the preclotting property due to the ultrafine fibers is particularly exhibited. Further, this pre-clotting property becomes more important in the case of a small-diameter artificial blood vessel, and its effect is particularly exhibited when the diameter is 6 mm or less.
本発明に用いられる極細繊維は、ポリエステル
系、コラーゲン系、ポリテトラフルオロエチレン
系、ポリウレタン系、ポリアミド系、レーヨン系
等の生体非吸収性、吸収性のもののいずれの目的
に応じ適宜使用可能である。特に吸収性のものを
使用する場合は骨格となる高透水率構造の織り、
編み、もしくは組紐に用いる繊維は生体非吸収性
の繊維とし両者の組み合わせた形で使用するのが
よい。本発明で生体吸収性の極細繊維が使用可能
な理由は、生体への植え込み後血管内に生体の擬
内膜が形成され血漏が防がられる時点まで、血漏
防止機能としてプリクロツテイング機能が作用し
てくれればよく、それ以降ではかかるプリクロツ
テイング形式に必要とされた極細繊維は必要とな
くなるためである。かかる生体非吸収性と吸収性
ポリマーの組み合わせとしては、例えばポリエス
テルとコラーゲン、ポリエステルとレーヨン、ポ
リテトラフルオロチレンとコラーゲン、レーヨン
などであるが、これはほんの１例であり、本発明
はこれに限定されるものではない。 The ultrafine fibers used in the present invention can be non-bioabsorbable or bioabsorbable fibers such as polyester, collagen, polytetrafluoroethylene, polyurethane, polyamide, rayon, etc. depending on the purpose. . In particular, when using absorbent materials, weaving with a high water permeability structure as the skeleton,
It is preferable that the fibers used for knitting or braiding be non-bioabsorbable fibers and a combination of the two. The reason why bioabsorbable ultrafine fibers can be used in the present invention is that after implantation into a living body, the preclotting function is used to prevent blood leakage until a biological pseudointima is formed in the blood vessel and blood leakage is prevented. This is because after that, the ultrafine fibers required for such preclotting method are no longer needed. Examples of such combinations of non-bioabsorbable and absorbable polymers include polyester and collagen, polyester and rayon, polytetrafluoroethylene and collagen, and rayon, but these are just examples, and the present invention is not limited to these. It is not something that will be done.
極細繊維を用いるに当たつては当初から極細の
ものを用いてもよいが、物理的もしくは化学的処
理により極細可能な繊維を用いチユーブ形成後極
細化してもよい。かかる極細可能繊維の例とし
て、例えば特公昭44−18369号公報や同様の例と
して特公昭46−3816号公報、特公昭53−37403号
公報などに記載されたもの、もしくはポリマーブ
レンド繊維等があり、２成分以上の成分の剥離、
あるいは少なくとも１成分の分解もしくは抽出除
去によつて極細化が可能なものである。 When using ultrafine fibers, they may be ultrafine from the beginning, or they may be made ultrafine after tube formation using fibers that can be made ultrafine through physical or chemical treatment. Examples of such ultra-fine fibers include those described in Japanese Patent Publication No. 44-18369, similar examples such as Japanese Patent Publication No. 46-3816 and Japanese Patent Publication No. 53-37403, and polymer blend fibers. , peeling of two or more components,
Alternatively, it can be made extremely fine by decomposing or extracting and removing at least one component.
チユーブ形成方法は通常の方法に従い、織り、
編み、組紐あるいは不織布の方法で容易に可能で
ある。特に細番手のヤーンを用いチユーブを形成
するのは作業性の点で極めて難しいが、本発明の
ごとく多成分系繊維を用い、当初は太い状態でチ
ユーブ加工しておき、加工後極細化処理（細番手
処理）するのが特に効果的である。本発明におい
て極細繊維のほかに、補強もしくはキンキング防
止等のための通常のこれより太い繊度と組み合わ
せてもよい。しかし1dtex以下の極細繊維を用い
ることにより細胞形成が著しく促進され、また表
面に用いた場合は表面の初期フイブリン層、ある
いは擬内膜の厚さが大幅に薄く均一となり、特に
細口径の場合に有利である。さらに好ましい態様
としては、かかる極細繊維の利用のみならずより
空隙の多い構造即ち高透水率とすることによりよ
り薄く均一な内皮膜の形成が可能となる。本発明
では低透水率でも効果があるが、よりその特徴が
発揮されるのは高透水率の場合であり、前述透水
率で例えば600以上好ましくは1200以上さらには
2000以上6000ml／min・cm2・120mmHg以下のよう
な場合である。 The tube formation method follows the usual method, weaving,
This is easily possible by knitting, braiding or non-woven methods. In particular, it is extremely difficult to form tubes using fine count yarn in terms of workability, but as in the present invention, multi-component fibers are used and the tubes are initially processed in a thick state, and then processed to become ultra-fine. It is particularly effective to perform fine-grain treatment. In the present invention, in addition to the ultra-fine fibers, it may be combined with ordinary fibers having a fineness larger than this for reinforcement or prevention of kinking. However, by using microfibers of 1 dtex or less, cell formation is significantly promoted, and when used on the surface, the thickness of the initial fibrin layer or pseudointima on the surface becomes significantly thinner and more uniform, especially when the diameter is small. It's advantageous. In a more preferred embodiment, it is possible to form a thinner and more uniform endothelial membrane not only by using such ultrafine fibers but also by creating a structure with more voids, that is, a higher water permeability. Although the present invention is effective even with a low water permeability, its characteristics are best exhibited when the water permeability is high.
This is a case of 2000 or more and 6000ml/min・cm 2・120mmHg or less.
また、本発明では口径６mm以下の場合に有効で
あり、従来６mmφ以下のこのような高水率の場合
はプリクロツテイングは極めて難しかつたが、本
発明のごとき構造とすることでこのプリクロツテ
イングも容易に均一に行え、薄い均一な内皮膜形
成が可能となり細口径での血栓閉塞も著しく軽減
されるのである。 In addition, the present invention is effective when the diameter is 6 mm or less, and conventionally it was extremely difficult to perform pre-clotting in the case of diameters of 6 mm or less and such high water rates, but with the structure of the present invention, this pre-clotting is possible. Teing can also be easily and uniformly performed, making it possible to form a thin and uniform endothelial membrane, and significantly reducing thrombotic occlusion at small diameters.
このプリクロツテイングをより容易に行わしめ
る手段として、例えば、人工血管内部に、その径
に見合つた、かつ人工血管素材に比し、凝固血液
との剥離性の良い状態もしくは物質からなるチユ
ーブ、棒、パイプなど、例えば、フツ素系、ポリ
アセタール系、シリコーン系、ポリオレフイン系
などからなるもの、あるいは表面コーテイングし
て凝固血液との剥離性を上げたチユーブ、パイ
プ、棒などを挿入した状態でプリクロツテイング
を行い完了後挿入物を抜き取る方法が極めて効果
的であり、一般に広く推奨できる画期的な方法で
ある。本発明でもこの方法は有効に活用できる。 As a means to perform this pre-clotting more easily, for example, a tube or a rod made of a material or material suitable for the diameter of the artificial blood vessel and which has better releasability from coagulated blood than the artificial blood vessel material can be placed inside the artificial blood vessel. , pipes, etc., made of fluorine-based, polyacetal-based, silicone-based, polyolefin-based, etc., or tubes, pipes, rods, etc. whose surface has been coated to improve releasability from coagulated blood. The method of removing the inserted material after the insertion is completed is extremely effective and is an innovative method that can be widely recommended to the general public. This method can also be effectively utilized in the present invention.
本発明では極細繊維と通常の太い繊維との組み
合わせでも良好な結果を示す場合が多いが、より
好ましい場合は総て極細繊維からなるものであ
る。 In the present invention, a combination of ultrafine fibers and ordinary thick fibers often shows good results, but more preferably the fibers are made entirely of ultrafine fibers.
［実施例］
実施例 １
経糸55Dtex−48fのポリエチレンテレフタレー
ト、緯糸に128Dtex−32f多芯型複合繊維（高分
子配列体）で島数16／ｆのもを用いて平織組織で
チユーブを作製した。このとき用いた高分子配列
体繊維には海成分ポリスチレン20部、島成分ポリ
エチレンテレフタレート80部であつた。このチユ
ーブの上から、別途同一の高分子配列体繊維を用
い形成した７ｇ／m2のウエツプを巻きウオーター
ジエツトパンチ処理を行つた。この後トルエン中
に浸け、次いでクリンプ付与処理を行つた。この
人工血管は第１図の如く0.2dtexの極細繊維が繊
組織の空間部にランダムに薄く散在していた。ま
た、内径は６mmφで透水率は3100ml／min・cm2・
120mlHgであつた。この人工血管に太さ約６mmの
ステンレスの棒にシリコーンゴムをコートした棒
を挿入し、犬の血液を用いプリクロツテイング処
理をしたところ、極めて均一に良好なプリクロツ
テイングを行うことができた。この処理をした人
工血管を用いた犬に植え込みテストをしたとこ
ろ、45日ですでに良好な厚さ20μmの極めて均一
な擬内膜形成がみられ画期的効果が確認された。[Examples] Example 1 A tube was fabricated with a plain weave structure using polyethylene terephthalate with warp yarns of 55Dtex-48f and 128Dtex-32f multifilamentary composite fibers (polymer array) with an island number of 16/f in the weft yarns. The polymer array fiber used at this time contained 20 parts of sea component polystyrene and 80 parts of island component polyethylene terephthalate. A 7 g/m 2 web separately formed using the same polymer array fibers was wrapped over the tube and waterjet punched. After that, it was immersed in toluene and then subjected to a crimp treatment. As shown in Fig. 1, this artificial blood vessel had ultrafine fibers of 0.2 dtex thinly and randomly scattered in the spaces of the fibrous tissue. In addition, the inner diameter is 6mmφ and the water permeability is 3100ml/min・cm 2・
It was 120mlHg. When a stainless steel rod approximately 6 mm thick coated with silicone rubber was inserted into this artificial blood vessel and a preclotting process was performed using dog blood, very uniform and good preclotting was achieved. . When an artificial blood vessel treated with this treatment was implanted into dogs and tested, an extremely uniform pseudoendometrium formation with a thickness of 20 μm was observed within 45 days, confirming the revolutionary effect.
比較例 １
経糸と緯糸ともに実施例１と同じ糸使いで同様
の手段で密度の異なる、また実施例１の真綿状の
ウエツプを用いないチユーブを形成し、透水率が
実施例１に最も近い2900ml／min・cm2・120mlHg
のものを選び、同様にプリクロツテイング処理し
犬の体内に植え込んだ。このもの、織密度が粗
く、織目空間部が大きく、この部分に血液のため
の核となる極細繊維が存在しないものであつて、
プリクロツテイングは人工血管の孔が大きいため
かなりの技術を要し、実施例１程の薄く均一な状
態とはならなかつた。犬のテストでも植え込み後
出血がみられ血漏防止性も十分ではなかつた。Comparative Example 1 A tube was formed using the same warp and weft yarns as in Example 1, using the same method to form a tube with different densities, and without using the cotton-like wep of Example 1, and having a water permeability of 2900 ml, which was the closest to that of Example 1. /min・cm2・120mlHg
One of these was selected, treated with preclocution, and implanted into the dog's body. This material has a coarse weave density, a large weave space, and there are no ultrafine fibers that serve as a nucleus for blood in this part,
Pre-clotting required a considerable amount of skill because the pores of the artificial blood vessel were large, and the thin and uniform state as in Example 1 was not achieved. Bleeding after implantation was also observed in tests on dogs, and the ability to prevent blood leakage was not sufficient.
実施例 ２
高分子配列体繊維で55Dtex−24f、島数36、島
成分ポリエチレンテレフタレート30部、海成分共
重合ポリエステル70部のものを経糸、緯糸に用
い、平組織でチユーブＡを形成した。さらに別途
経糸55Dtex−48fの通常のポリエチレンテレフタ
レート繊維、緯糸に55Dtex−98fの通常のポリエ
チレンテレフタレート繊維を用い５枚繻子組織で
袋織りしチユーブＢを形成した。既に準備したチ
ユーブＡを4.2mmφのステンレス棒に通し、この
上から後のチユーブＢを被せ２％のカセイソーダ
液で60℃×20分処理し、中和し水洗後さらにクリ
ンプ加工した。このチユーブの織り密度は、内面
は経×緯密度＝120×135本／inである（実際はヤ
ーンを構成するフイラメント１本が更に36本に分
かれているためフイラメント繊維の密度でいえ
ば、この36倍の本数のものとなる）極めて高密度
のものにもかかわらず細番手のため比較的空間の
あるものであつた。外側は経×緯＝46×50本／in
と極めて粗いものである。この人工血管は外側の
組織の粗い空間部に内側の細番手の0.02dtexの極
細繊維が交錯して存在していた。またこの人工血
管の透水率は1800ml／min・cm2・120mmHgであ
り、犬に植え込むに当たりプリクロツテイング性
は極めて良好であつた。また吻合性も柔軟で極め
て良くほつれも殆ど見られなかつた。治癒経過は
85日で内面全体に及ぶ内膜形成がみられ極めて良
好な結果を示した。Example 2 A polymer array fiber of 55Dtex-24f, 36 islands, 30 parts of island component polyethylene terephthalate, and 70 parts of sea component copolyester was used for the warp and weft, and a tube A was formed with a flat structure. Furthermore, a tube B was formed by bag weaving with a five-ply sateen weave using ordinary polyethylene terephthalate fibers of 55Dtex-48f for the warp and ordinary polyethylene terephthalate fibers of 55Dtex-98f for the weft. The already prepared tube A was passed through a stainless steel rod of 4.2 mm diameter, and the tube B was placed over it and treated with a 2% caustic soda solution at 60° C. for 20 minutes, neutralized, washed with water, and further crimped. The weave density of this tube is warp x weft density = 120 x 135 fibers/in on the inner surface (actually, one filament that makes up the yarn is further divided into 36 fibers, so in terms of filament fiber density, this is 36 fibers/in). Even though it was extremely dense (double the number of pieces), it had a relatively large amount of space because of its fine count. Outside is longitude x latitude = 46 x 50 pieces/in
It is extremely rough. In this artificial blood vessel, ultrafine fibers with a fine count of 0.02 dtex were intertwined with each other in the rough space of the outer tissue. Furthermore, the water permeability of this artificial blood vessel was 1800 ml/min·cm 2 ·120 mmHg, and the pre-clotting property was extremely good when implanted in a dog. In addition, the anastomosis was flexible and extremely good, with almost no fraying observed. The healing process
Intima formation covering the entire inner surface was observed after 85 days, showing extremely good results.
［発明の効果］
本発明の構造の人口血管とすることにより、プ
リクロツテイング性に優れ、薄く良好なプリクロ
ツテイングと薄く均一な肉皮膜の早期形成が可能
となり取扱性と生体適合性を同時に満足する画期
的な人口血管が得られる。[Effects of the Invention] The artificial blood vessel having the structure of the present invention has excellent preclotting properties, enables thin and good preclotting and early formation of a thin and uniform skin membrane, and achieves ease of handling and biocompatibility at the same time. A satisfying and innovative artificial blood vessel can be obtained.
第１図、第２図に本発明を理解するための一助
として、いずれも概念図により本発明による人工
血管の構造の１例を示した。第１図は太番手より
なる目の粗い織組織の間に極細繊維が薄く分繊し
て実質的に透水率を低下させずにプリクロツテイ
ング性を上げられるような構造となつているもの
である。第２図は極細繊維よりなる細番手の目の
細かい内面のチユーブＡの上に太番手の目の粗い
チユーブＢが形成された２重構造となつているも
のである。
１……目の粗い織組織、２……極細繊維、３…
…チユーブＢ、４……チユーブＡ。
As an aid to understanding the present invention, FIGS. 1 and 2 each show an example of the structure of an artificial blood vessel according to the present invention using conceptual diagrams. Figure 1 shows a structure in which ultra-fine fibers are thinly separated between coarse woven structures made of thick yarns to improve pre-clotting properties without substantially reducing water permeability. be. FIG. 2 shows a double structure in which a thick inner tube B with a coarse mesh is formed on a fine inner tube A with a fine mesh made of ultra-fine fibers. 1... Coarse weave structure, 2... Ultrafine fiber, 3...
...Tube B, 4...Tube A.
Claims (1)
し、透水率が600ml／min・cm2・120mmHg以上の
人工血管において、該基本構造の組織目の空間部
に、1dtex以下の極細繊維が薄く存在した状態を
有してなることを特徴とする生体適合性とプリク
ロツテイング性に優れた人工血管。 ２ 織り、編み、あるいは組紐等の基本構造を有
し、透水率が600ml／min・cm2・120mmHg以上の
人工血管において、該人工血管が極細繊維を含む
多重組織からなり、少なくとも細繊度の目の細か
い層とそれよりも太繊度で目の粗い層とから構成
されてなるとともに、前記太繊度の基本構造の組
繊目の空間部には、1dtex以下の極細繊維が薄く
存在した状態を有してなることを特徴とする生体
適合性とプリクロツテイング性に優れた人工血
管。[Scope of Claims] 1. In an artificial blood vessel having a basic structure such as weaving, knitting, or braiding, and having a water permeability of 600 ml/min・cm 2・120 mmHg or more, 1 dtex is added to the space of the tissue of the basic structure. An artificial blood vessel having excellent biocompatibility and pre-clotting properties, characterized by having a thin layer of the following ultrafine fibers. 2 Artificial blood vessels that have a basic structure such as weaving, knitting, or braiding, and have a water permeability of 600 ml/min・cm 2・120 mmHg or more, are made of multiple tissues containing ultrafine fibers, and have at least an eye of fineness. It is composed of a fine layer and a coarser layer with a thicker fineness than that, and has a state in which ultrafine fibers of 1 dtex or less are thinly present in the spaces between the interwoven fibers of the basic structure of the thick fineness. An artificial blood vessel with excellent biocompatibility and pre-clotting properties.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61260719A JPS63115555A (en) | 1986-11-04 | 1986-11-04 | Artificial blood vessel excellent in living body compatibility and preclotting property |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61260719A JPS63115555A (en) | 1986-11-04 | 1986-11-04 | Artificial blood vessel excellent in living body compatibility and preclotting property |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS63115555A JPS63115555A (en) | 1988-05-20 |
| JPH0588611B2 true JPH0588611B2 (en) | 1993-12-22 |
Family
ID=17351807
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP61260719A Granted JPS63115555A (en) | 1986-11-04 | 1986-11-04 | Artificial blood vessel excellent in living body compatibility and preclotting property |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS63115555A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2014168198A1 (en) | 2013-04-12 | 2014-10-16 | 東レ株式会社 | Antithrombotic artificial blood vessel |
| WO2014168197A1 (en) | 2013-04-12 | 2014-10-16 | 東レ株式会社 | Antithrombotic artificial blood vessel |
| US10251742B2 (en) | 2014-02-12 | 2019-04-09 | Toray Industries, Inc. | Artificial blood vessel |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4726402B2 (en) * | 2003-06-13 | 2011-07-20 | 泰晴 野一色 | Luminogenesis-inducing material |
| AU2015302742A1 (en) * | 2014-08-12 | 2017-02-09 | Toray Industries, Inc. | Vascular prothesis |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6077764A (en) * | 1983-10-05 | 1985-05-02 | 東レ株式会社 | Artificial blood vessel |
-
1986
- 1986-11-04 JP JP61260719A patent/JPS63115555A/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6077764A (en) * | 1983-10-05 | 1985-05-02 | 東レ株式会社 | Artificial blood vessel |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2014168198A1 (en) | 2013-04-12 | 2014-10-16 | 東レ株式会社 | Antithrombotic artificial blood vessel |
| WO2014168197A1 (en) | 2013-04-12 | 2014-10-16 | 東レ株式会社 | Antithrombotic artificial blood vessel |
| EP2985041A4 (en) * | 2013-04-12 | 2016-10-19 | Toray Industries | Antithrombotic artificial blood vessel |
| EP2985042A4 (en) * | 2013-04-12 | 2016-10-19 | Toray Industries | Antithrombotic artificial blood vessel |
| US10251742B2 (en) | 2014-02-12 | 2019-04-09 | Toray Industries, Inc. | Artificial blood vessel |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS63115555A (en) | 1988-05-20 |
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