JP2003159333A - Core material for guide wire for medical treatment and guide wire for medical treatment - Google Patents
Core material for guide wire for medical treatment and guide wire for medical treatmentInfo
- Publication number
- JP2003159333A JP2003159333A JP2001361033A JP2001361033A JP2003159333A JP 2003159333 A JP2003159333 A JP 2003159333A JP 2001361033 A JP2001361033 A JP 2001361033A JP 2001361033 A JP2001361033 A JP 2001361033A JP 2003159333 A JP2003159333 A JP 2003159333A
- Authority
- JP
- Japan
- Prior art keywords
- guide wire
- core material
- wire
- medical guide
- insertion portion
- 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.)
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Links
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、治療や検査を必要
とする血管、消化管、気管、その他体腔（以下、要治療
管という）内に導入する細い管状のカテーテルを案内す
るのに用いる医療用ガイドワイヤ用芯材（以下、芯材と
もいう）及び医療用ガイドワイヤ（以下、ガイドワイヤ
ともいう）に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to medical treatment used for guiding a thin tubular catheter to be introduced into a blood vessel, digestive tract, trachea, or other body cavity (hereinafter referred to as a treatment-necessary tube) that requires treatment or inspection. The present invention relates to a guide wire core material (hereinafter, also referred to as a core material) and a medical guide wire (hereinafter, also referred to as a guide wire).
【０００２】[0002]
【従来の技術】ガイドワイヤの構造は用途に応じて種々
のものがあるが、一般的には、図３（ａ）に示すよう
に、所定長さの芯材１０の周囲を合成樹脂１１で被覆し
たものと、図３（ｂ）に示すように、所定長さの芯材１
２の周囲をコイルスプリング１３で被包したものとがあ
る。そして、図３（ａ）（ｂ）に示すように、芯材１０
と１２にはガイドワイヤとしての挿入部分に柔軟性を付
与するため、挿入部１０ａと１２ａは次第に断面積が減
少する先細形状に形成されている。2. Description of the Related Art Although there are various guide wire structures depending on the intended use, generally, as shown in FIG. 3 (a), a synthetic resin 11 surrounds a core material 10 of a predetermined length. As shown in FIG. 3 (b), the coated material and the core material 1 having a predetermined length
There is one in which the circumference of 2 is covered with a coil spring 13. Then, as shown in FIGS. 3A and 3B, the core material 10
Insertions 10a and 12a are formed in a tapered shape whose cross-sectional area gradually decreases in order to give flexibility to the insertion portions as guide wires.
【０００３】上記芯材には、ステンレス鋼線またはピア
ノ線が従来から用いられている。しかし、この種の芯材
を用いたガイドワイヤは、先端部分を先細形状にしても
柔軟性に欠け、複雑に蛇行する分岐血管等に対しては適
用し難いという問題があった。Conventionally, a stainless steel wire or a piano wire has been used as the core material. However, the guide wire using this type of core material has a problem that it is not flexible even if the tip portion is tapered, and it is difficult to apply it to a branching blood vessel that meanders in a complicated manner.
【０００４】そこで、芯材として、超弾性合金である、
（１）Ｔｉ−Ｎｉ−Ｆｅ系合金を用いたガイドワイヤ
（例えば、特公平４−２２７３号公報）、（２）Ｔｉ−
Ｎｉ系合金を用いたガイドワイヤ（例えば、特公平４−
８０６５号公報）、（３）Ｃｏ−Ｎｉ−Ｃｒ−Ｆｅ系合
金を用いたガイドワイヤ（例えば、特開平６−６３１５
１号公報）等が提案されている。Therefore, the core material is a superelastic alloy,
(1) A guide wire using a Ti-Ni-Fe alloy (for example, Japanese Patent Publication No. 4-2273), (2) Ti-
A guide wire using a Ni-based alloy (for example, Japanese Patent Publication No. 4-
8065), (3) a guide wire using a Co-Ni-Cr-Fe-based alloy (for example, Japanese Patent Laid-Open No. 6-6315).
No. 1) has been proposed.
【０００５】ここで、超弾性とは、特開平６−６３１５
１号公報第１欄第５０行〜第２欄第７行にも記載されて
いるように、回復可能な弾性歪みが数％から数十％と大
きく、しかも歪みが増加しても荷重の大きさが変わらな
いという特性を意味する。Here, the term "superelasticity" means Japanese Patent Laid-Open No. 6-6315.
As described in column 1, line 50 to column 2, line 7 of Japanese Patent Publication No. 1, the recoverable elastic strain is as large as several% to several tens%, and the load is large even if the strain increases. It means that the characteristics do not change.
【０００６】上記超弾性合金からなる芯材は、柔軟でか
なりの範囲までの変形（約８％の歪み）に対しても復元
性を有するため、手元操作中、折れ曲がりが生じ難く、
且つ曲がりぐせがつきにくいなどの利点を有している。Since the core material made of the above-mentioned superelastic alloy is flexible and has a restoring property to a deformation to a considerable extent (strain of about 8%), it is hard to be bent during the hand operation.
Moreover, it has an advantage that it is hard to bend.
【０００７】[0007]
【発明が解決しようとする課題】ところで、ガイドワイ
ヤとして重要な性能は、手元操作によって要治療管内に
スムーズに挿入できて、カテーテルを目的部位に正確に
案内導入できることである。このため、ガイドワイヤに
用いる芯材には、挿入部が複雑に蛇行する要治療管に対
応し、且つ要治療管の内壁を傷つけることなく挿入し得
る形態順応性を備え、これに続く導入部が手元での微妙
な操作量でも挿入部に正確に伝達するトルク伝達性を備
えていることが要求されている。By the way, the important performance of the guide wire is that it can be smoothly inserted into the treatment-needed tube by manual operation, and the catheter can be accurately guided and introduced into the target site. Therefore, the core material used for the guide wire has a conformability that allows the insertion portion to be complicatedly meandering and needs to be inserted without damaging the inner wall of the treatment-requiring tube. Is required to have torque transmissibility that accurately transmits to the insertion portion even with a delicate operation amount at hand.
【０００８】そして、今日、医療技術の発達に応じて、
複雑な分岐血管に対しても適用できるようにするため、
ガイドワイヤの芯材には、挿入部の形態順応性と導入部
のトルク伝達性を、より一層向上することが求められて
いる。[0008] Today, with the development of medical technology,
In order to be applicable to complex branch vessels,
The core material of the guide wire is required to further improve the conformability of the insertion portion and the torque transmissibility of the introduction portion.
【０００９】しかし、上記（１）および（３）の芯材を
用いたガイドワイヤは、芯材が超弾性合金の単一材料か
らなるため、全体として、超弾性があって形態順応性を
充分に備えているが、伝達可能トルク及びねじり剛性が
ステンレス鋼線またはピアノ線に比較して劣るため、導
入部のトルク伝達性に難点がある。However, in the guide wire using the core material of the above (1) and (3), the core material is made of a single material of a superelastic alloy, so that it has superelasticity as a whole and is sufficiently conformable. However, since the transmissible torque and the torsional rigidity are inferior to those of the stainless steel wire or the piano wire, there is a problem in the torque transmissibility of the introduction portion.
【００１０】また、上記（２）の芯材を用いたガイドワ
イヤは、超弾性合金の単一材料で構成した芯材の挿入部
と導入部の熱処理条件を変えることにより、挿入部に形
態順応性を付与し、導入部にトルク伝達性を付与したも
のであるが、高価な超弾性合金を用いて熱処理している
ため、材料コストおよび処理コストが高くなり、製造コ
ストが上昇する。The guide wire using the core material of the above (2) conforms to the insertion portion by changing the heat treatment conditions of the insertion portion and the introduction portion of the core material made of a single superelastic alloy material. However, since the heat treatment is performed using an expensive superelastic alloy, the material cost and the processing cost increase, and the manufacturing cost increases.
【００１１】本発明は従来の技術の有するこのような問
題点に鑑みてなされたものであって、その目的は、挿入
部に適度の柔軟性を有し且つ導入部に適度の剛性を備え
ることにより優れた操作性を有する、高品質で低コスト
の医療用ガイドワイヤ用芯材および医療用ガイドワイヤ
を提供することにある。The present invention has been made in view of the above problems of the prior art, and an object thereof is to provide the insertion portion with appropriate flexibility and the introduction portion with appropriate rigidity. Accordingly, it is an object of the present invention to provide a high-quality, low-cost core material for a medical guide wire and a medical guide wire having superior operability.
【００１２】[0012]
【課題を解決するための手段】上記目的を達成するため
に本発明の医療用ガイドワイヤ用芯材は、挿入部が形態
順応性を備え、導入部がトルク伝達性を備えた芯材であ
って、上記挿入部と導入部とを化学組成の異なる線材で
構成し、且つ挿入部と導入部を一体に接合したことを特
徴としている。In order to achieve the above object, the core material for a medical guide wire according to the present invention is a core material in which the insertion part has conformability and the introduction part has torque transmission properties. In addition, the insertion portion and the introduction portion are made of wires having different chemical compositions, and the insertion portion and the introduction portion are integrally joined.
【００１３】ここで、形態順応性とは、複雑な分岐血管
にも内壁を傷つけることなく容易に挿入しうる特性を意
味し、トルク伝達性とは、微妙な手元操作量を先端部
（挿入部）に正確に伝達し得る特性を意味し、具体的に
は、挿入部を、Ｔｉ−Ｎｉ系合金、Ｃｕ−Ａｌ−Ｎｉ系
合金またはＦｅ−Ｎｉ−Ｃｏ−Ｔｉ系合金の線材で構成
し、導入部を、ステンレス鋼またはＣｏ−Ｎｉ−Ｃｒ−
Ｆｅ系合金の線材で構成することによって、上記特性を
達成することができる。Here, the morphological adaptability means a characteristic that even a complicated branch blood vessel can be easily inserted without damaging the inner wall, and the torque transmissibility means a delicate hand operation amount at the tip (insertion portion). ) Means that it can be accurately transmitted, specifically, the insertion portion is composed of a wire rod of Ti-Ni alloy, Cu-Al-Ni alloy or Fe-Ni-Co-Ti alloy, The introduction part is made of stainless steel or Co-Ni-Cr-
The above-mentioned characteristics can be achieved by using a wire of an Fe-based alloy.
【００１４】挿入部と導入部とは、各種接着材で接合し
てもよいが、それぞれの部分を構成する線材と親和性を
有するろう接合金を介して接合するのが好ましい。The insertion portion and the introduction portion may be joined by various adhesives, but it is preferable that they be joined through a brazing filler metal having an affinity with the wire material forming each portion.
【００１５】上記ろう接合金としては、Ｂを含有する銀
ろう、Ｎｉ箔、またはＢとＳｉを含有し残部がＮｉから
なるアモルファス箔が好ましい。The brazing alloy is preferably silver braze containing B, Ni foil, or amorphous foil containing B and Si with the balance being Ni.
【００１６】上記芯材を用いて、合成樹脂や複合材料等
で被覆したり、コイルスプリングで被包することによ
り、医療用ガイドワイヤを構成することができる。A medical guide wire can be constructed by covering the core material with a synthetic resin, a composite material or the like, or enclosing it with a coil spring.
【００１７】[0017]
【発明の実施の形態】本発明の実施の形態を図面に基づ
いて説明する。BEST MODE FOR CARRYING OUT THE INVENTION Embodiments of the present invention will be described with reference to the drawings.
【００１８】図１において、所定の長さ（例えば、２０
００〜３０００mm）を有する医療用ガイドワイヤ用芯材
１は、挿入部２と導入部３とを接合部４で一体に接合し
てなり、挿入部２と導入部３とは、挿入部２の弾性限度
が導入部３の弾性限度より大きく、導入部３のねじり剛
性が挿入部２のねじり剛性より大きくなるような関係を
満たすように、化学組成の異なる線材で構成されてい
る。In FIG. 1, a predetermined length (for example, 20
The core material 1 for a medical guide wire having a diameter of 0 to 3000 mm is formed by integrally joining the insertion portion 2 and the introduction portion 3 at the joint portion 4, and the insertion portion 2 and the introduction portion 3 are Wires having different chemical compositions are formed so that the elastic limit is larger than the elastic limit of the introducing portion 3 and the torsional rigidity of the introducing portion 3 is larger than the torsional rigidity of the inserting portion 2.
【００１９】挿入部２の長さは、特に限定されるもので
はないが、通常１００〜３００mm程度とする。さらに、
挿入部２の形状は導入部３と同一でもよいが、図１に示
すように、先端に向けて断面積が次第に減少する先細形
状に成形すると、より一層柔軟になり形態順応性を向上
することができる。The length of the insertion portion 2 is not particularly limited, but is usually about 100 to 300 mm. further,
The shape of the insertion portion 2 may be the same as that of the introduction portion 3, but as shown in FIG. 1, if the insertion portion 2 is formed in a tapered shape with the cross-sectional area gradually decreasing toward the tip, it becomes even more flexible and improves the conformability of the shape. You can
【００２０】挿入部２を構成する線材としては、Ｔｉ−
Ｎｉ系合金、Ｃｕ−Ａｌ−Ｎｉ系合金またはＦｅ−Ｎｉ
−Ｃｏ−Ｔｉ系合金から選択したいずれかの合金を用い
ることができる。そして、挿入部２としての必要な特性
を考慮すると、Ｔｉ−Ｎｉ系合金としては、Ｎｉ＝５０
〜５２原子％で残部がＴｉからなるもの、Ｃｕ−Ａｌ−
Ｎｉ系合金としては、Ａｌ＝１３〜１５原子％、Ｎｉ＝
３〜５原子％で残部がＣｕからなるもの、Ｆｅ−Ｎｉ−
Ｃｏ−Ｔｉ系合金としては、Ｎｉ＝３２〜３４原子％、
Ｃｏ＝１０〜１５原子％、Ｔｉ＝３〜６原子％で残部が
Ｆｅからなるものが好ましい。As the wire material forming the insertion portion 2, Ti-
Ni-based alloy, Cu-Al-Ni-based alloy or Fe-Ni
Any alloy selected from -Co-Ti alloys can be used. Then, considering the characteristics required for the insertion portion 2, as the Ti—Ni-based alloy, Ni = 50.
.About.52 atomic% and balance Ti, Cu--Al--
As a Ni-based alloy, Al = 13 to 15 atomic%, Ni =
Fe-Ni-, with 3 to 5 atomic% and the balance being Cu
As a Co-Ti alloy, Ni = 32 to 34 atomic%,
It is preferable that Co = 10 to 15 atomic%, Ti = 3 to 6 atomic%, and the balance being Fe.
【００２１】導入部３を構成する線材としては、ステン
レス鋼またはＣｏ−Ｎｉ−Ｃｒ−Ｆｅ系合金を用いるこ
とができる。そして、導入部３としての必要な特性を考
慮すると、ステンレス鋼としては、ＳＵＳ３０４、ＳＵ
Ｓ３１６、ＳＵＳ４０３、ＳＵＳ４１０、ＳＵＳ４２０
Ｊ２、ＳＵＳ３２９Ｊ１、ＳＵＳ６３０、ＳＵＳ６３１
などが好ましく、Ｃｏ−Ｎｉ−Ｃｒ−Ｆｅ系合金として
は、Ｎｉ＝９〜１１原子％、Ｃｒ＝１９〜２１原子％、
Ｆｅ＝３原子％以下で残部がＣｏからなるものが好まし
い。As the wire material forming the introducing portion 3, stainless steel or Co-Ni-Cr-Fe alloy can be used. Then, considering the characteristics required for the introduction part 3, as stainless steel, SUS304, SU
S316, SUS403, SUS410, SUS420
J2, SUS329J1, SUS630, SUS631
And the like, and as the Co-Ni-Cr-Fe-based alloy, Ni = 9 to 11 atomic%, Cr = 19 to 21 atomic%,
It is preferable that Fe = 3 atomic% or less and the balance be Co.
【００２２】挿入部２と導入部３を構成する線材は、用
途に応じて適宜組み合わせることができるが、Ｔｉ−Ｎ
ｉ系合金とステンレス鋼（例えば、ＳＵＳ３０４）の組
み合わせが低コスト化を図りうる点から好ましい。The wire rods forming the insertion portion 2 and the introduction portion 3 can be appropriately combined depending on the application, but Ti--N
A combination of an i-based alloy and stainless steel (for example, SUS304) is preferable from the viewpoint of cost reduction.
【００２３】挿入部２と導入部３とを溶接によって直接
接合すると、金属間化合物（例えば、ＦｅＴｉ）によ
り、接合部４が脆化することがあるので、挿入部２と導
入部３を構成する両方の線材に対して親和性を有する低
融点のろう接合金を介して挿入部２と導入部３を接合す
るのが好ましい。If the insertion portion 2 and the introduction portion 3 are directly joined by welding, the joint portion 4 may become brittle due to an intermetallic compound (eg, FeTi). Therefore, the insertion portion 2 and the introduction portion 3 are formed. It is preferable to join the insertion portion 2 and the introduction portion 3 through a low melting point brazing metal having affinity for both wire rods.
【００２４】上記ろう接合金としては、Ｂを３原子％含
有する銀ろう、Ｎｉ箔、または２〜４原子％のＢと２〜
４原子％のＳｉを含有し残部がＮｉからなるアモルファ
ス箔を用いることができる。これらのうち、挿入部２に
Ｔｉ−Ｎｉ系合金を用いると、その親和性の点でＮｉ箔
が好ましい。また、ろう接合金の厚みとしては、ねじり
剛性の点から、医療用ガイドワイヤ用芯材１の直径、す
なわち、挿入部２と導入部３の線材の直径（０．２〜
０．７mm程度）の１／３〜１／５程度が好ましい。As the brazing alloy, silver brazing alloy containing 3 atomic% of B, Ni foil, or 2 to 4 atomic% of B and 2 to 2 atomic% is used.
An amorphous foil containing 4 atomic% of Si and the balance of Ni can be used. Among these, when a Ti—Ni-based alloy is used for the insertion portion 2, Ni foil is preferable from the viewpoint of its affinity. Further, as the thickness of the brazing metal, from the viewpoint of torsional rigidity, the diameter of the medical guidewire core material 1, that is, the diameter of the wire rod of the insertion portion 2 and the introduction portion 3 (0.2 to
It is preferably about 1/3 to 1/5 of about 0.7 mm).
【００２５】挿入部２と導入部３との接合手段として
は、レーザ溶接または電子ビーム溶接を使用することが
できる。このうち、特に、通常の光に比較して単色性と
指向性がよく、位相が揃っており、極めて集光性がよい
という性質をもつレーザ光を利用したレーザ溶接が好ま
しい。というのは、エネルギー密度が非常に大きな微小
スポットにより、高精度溶接が可能となるからである。Laser welding or electron beam welding can be used as a joining means for the insertion portion 2 and the introduction portion 3. Of these, laser welding using laser light, which has a property of having good monochromaticity and directivity, uniform phase, and extremely good light-collecting property as compared with normal light, is particularly preferable. This is because minute spots with a very large energy density enable high-precision welding.
【００２６】以上のような芯材を用いた医療用ガイドワ
イヤは、図２（ａ）に示すように、医療用ガイドワイヤ
用芯材１の全体を合成樹脂５で被覆するか、または、図
２（ｂ）に示すように、挿入部２のみを合成樹脂５で被
覆することによって得ることができる。合成樹脂として
は、ポリエチレン、ポリエステル、ポリプロピレン、ポ
リウレタン、シリコーンゴム等の公知の材料を使用する
ことができる。In the medical guide wire using the core material as described above, as shown in FIG. 2 (a), the entire core material 1 for the medical guide wire is coated with the synthetic resin 5, or As shown in FIG. 2 (b), it can be obtained by covering only the insertion part 2 with the synthetic resin 5. As the synthetic resin, known materials such as polyethylene, polyester, polypropylene, polyurethane and silicone rubber can be used.
【００２７】[0027]
【実施例】以下に、本発明の実施例を説明する。導入部
材として、ＳＵＳ３０４組成の合金を真空炉で溶解し、
鍛造後、１１００℃以上の温度で熱間圧延を行い、線径
５mmに圧延した。次に、この圧延材を１０５０℃で焼鈍
後急冷し、加工率２０％の冷間伸線と焼鈍を繰り返して
０．７mmの線材とした。その後、１０５０℃で溶体化処
理後、加工率８２％で０．３mmに最終冷間伸線後、５０
０℃のＡｒ雰囲気中で３０秒間時効処理を施した。EXAMPLES Examples of the present invention will be described below. As an introduction member, an alloy of SUS304 composition is melted in a vacuum furnace,
After forging, hot rolling was performed at a temperature of 1100 ° C. or higher, and the wire diameter was 5 mm. Next, this rolled material was annealed at 1050 ° C. and then rapidly cooled, and cold drawing and annealing at a working rate of 20% were repeated to obtain a 0.7 mm wire material. Then, after solution heat treatment at 1050 ° C, the final cold drawing to 0.3 mm at a working rate of 82%, and then 50
Aging treatment was performed for 30 seconds in an Ar atmosphere at 0 ° C.
【００２８】一方、挿入部材として、Ｎｉ５１原子％で
残部がＴｉからなるＴｉ−Ｎｉ系合金を真空炉で溶解
し、鍛造後、８００℃以上の温度で熱間圧延を行い、線
径５mmに圧延した。次に、この圧延材を８００℃で焼鈍
後急冷し、加工率２０％の冷間伸線と焼鈍を繰り返して
０．４mmの線材とした。その後、８００℃で溶体化処理
後、加工率４４％で０．３mmに最終冷間伸線後、４００
℃のＡｒ雰囲気中で２分間時効処理を施した。On the other hand, as an insert member, a Ti-Ni alloy containing 51 atomic% of Ni and the balance of Ti was melted in a vacuum furnace, forged, and then hot-rolled at a temperature of 800 ° C. or higher, and rolled to a wire diameter of 5 mm. did. Next, this rolled material was annealed at 800 ° C. and then rapidly cooled, and cold drawing and annealing at a working rate of 20% were repeated to obtain a wire material of 0.4 mm. Then, after solution heat treatment at 800 ℃, final cold drawing to 0.3mm at a working rate of 44%, 400
Aging treatment was performed for 2 minutes in an Ar atmosphere at 0 ° C.
【００２９】次に、０．３mmのＴｉＮｉ線材とＳＵＳ３
０４線材との間に厚さ０．１mmのＮｉ箔を挿入し、線径
０．３mmのＴｉＮｉ線材とＳＵＳ３０４線材の両方に対
して、Ｎｉ箔に向かって僅かな力を加えてＮｉ箔を固定
し、その上からＹＡＧレーザ溶接機を用いてＮｉ箔を含
む接合部付近にレーザ照射し、ＴｉＮｉ線材とＳＵＳ３
０４線材とをレーザ溶接により接合し、図１に示すよう
な医療ガイドワイヤ用芯材１を得た。なお、この溶接
時、Ｎｉ箔の温度が約１４５０℃（Ｎｉの融点）にな
り、かつＴｉＮｉ線材とＳＵＳ３０４線材とが直接固溶
しないように、レーザの焦点を多少ぼかして照射した。Next, 0.3 mm TiNi wire and SUS3
Insert a 0.1 mm thick Ni foil between the 04 wire rod and fix the Ni foil by applying a slight force toward both the NiNi wire rod and the SUS304 wire rod with a wire diameter of 0.3 mm. Then, the vicinity of the joint including the Ni foil is laser-irradiated from above using a YAG laser welding machine, and the TiNi wire and SUS3 are welded.
The No. 04 wire was joined by laser welding to obtain a core material 1 for a medical guide wire as shown in FIG. During this welding, the focus of the laser was slightly blurred so that the temperature of the Ni foil became about 1450 ° C. (melting point of Ni) and the TiNi wire and the SUS304 wire did not directly form a solid solution.
【００３０】また、比較例１として、上記と同様の方法
で製造した線径０．３mmのＴｉＮｉ線材と同じ線径０．
３mmのＴｉＮｉ線材との間に厚さ０．１mmのＮｉ箔を挿
入し、２本の線径０．３mmのＴｉＮｉ線材に対して、Ｎ
ｉ箔に向かって僅かな力を加えてＮｉ箔を固定し、その
上からＹＡＧレーザ溶接機を用いてＮｉ箔を含む接合部
付近にレーザ照射し、ＴｉＮｉ線材同士をレーザ溶接に
より接合した。なお、この溶接時、Ｎｉ箔の温度が約１
４５０℃（Ｎｉの融点）になり、かつＴｉＮｉ線材が直
接固溶しないように、レーザの焦点を多少ぼかして照射
した。As Comparative Example 1, a TiNi wire rod having a wire diameter of 0.3 mm and a wire diameter of 0.
Insert a 0.1 mm thick Ni foil between the 3 mm TiNi wire and the two NiNi wires with a diameter of 0.3 mm.
The Ni foil was fixed by applying a slight force toward the i foil, and the vicinity of the joint including the Ni foil was irradiated with laser using a YAG laser welding machine, and the TiNi wires were joined by laser welding. The temperature of the Ni foil was about 1 during this welding.
Irradiation was performed by slightly blurring the laser focus so that the temperature became 450 ° C. (melting point of Ni) and the TiNi wire rod did not directly form a solid solution.
【００３１】さらに、比較例２として、上記と同様の方
法で、線径０．３mmのＴｉＮｉ線材単体のものも製造し
た。Further, as Comparative Example 2, a TiNi wire alone having a wire diameter of 0.3 mm was manufactured by the same method as described above.
【００３２】そして、上記のようにして得た本発明の医
療用ガイドワイヤ用芯材と比較例のものにおいて、伝達
可能トルクとねじり剛性比を測定した結果を以下の表１
に示す。Then, the results of measuring the transmissible torque and the torsional rigidity ratio of the core material for a medical guide wire of the present invention and the comparative example obtained as described above are shown in Table 1 below.
Shown in.
【００３３】[0033]
【表１】 [Table 1]
【００３４】「伝達可能トルク」とは、素材の先端をト
ルク計で保持し、基端部からねじり変形を与えた後、こ
の変形を解除して永久ねじり変形が発生していないこと
を確認した後、さらに大きな変形を与えることを繰り返
して、永久ねじり変形が発生しない最大トルクをいう。The term "transmittable torque" means that the tip of the material is held by a torque meter, and after the base end is twisted and deformed, this deformation is released to confirm that permanent twisting is not generated. After that, the maximum torque at which permanent torsional deformation does not occur is repeated by further applying a larger deformation.
【００３５】「ねじり剛性比」とは、所定のトルクを加
えたときのねじれ角度を、比較例１を１としたときの指
数で示したものである。The "torsional rigidity ratio" is an index when the torsion angle when a predetermined torque is applied is set to 1 in Comparative Example 1.
【００３６】表１に明らかなように、本発明の医療用ガ
イドワイヤ用芯材は、比較例１、２のものに比べて伝達
可能トルクとねじり剛性比が極めて大きく、トルク伝達
性に優れていることが分かる。As is clear from Table 1, the core material for a medical guide wire of the present invention has an extremely large transmissible torque and torsional rigidity ratio as compared with those of Comparative Examples 1 and 2, and is excellent in torque transmissibility. I know that
【００３７】[0037]
【発明の効果】本発明によれば、挿入部に適度の柔軟性
を有し且つ導入部に適度の剛性を備えることにより優れ
た操作性を有する、高品質で低コストの医療用ガイドワ
イヤ用芯材および医療用ガイドワイヤを提供することが
できる。EFFECTS OF THE INVENTION According to the present invention, a medical guide wire of high quality and low cost, which has an excellent operability by having an appropriate flexibility in the insertion portion and an appropriate rigidity in the introduction portion, is provided. A core material and a medical guide wire can be provided.
【図１】本発明の医療用ガイドワイヤ用芯材の断面図で
ある。FIG. 1 is a cross-sectional view of a core material for a medical guide wire according to the present invention.
【図２】図２（ａ）、（ｂ）は本発明の医療用ガイドワ
イヤの断面図である。2 (a) and 2 (b) are cross-sectional views of the medical guide wire of the present invention.
【図３】従来の医療用ガイドワイヤの断面図である。FIG. 3 is a cross-sectional view of a conventional medical guide wire.
１…医療用ガイドワイヤ用芯材 ２…挿入部 ３…導入部 ４…接合部 ５…合成樹脂 1 ... Core material for medical guide wire 2 ... insertion part 3 ... Introduction 4 ... Joint 5 ... Synthetic resin
───────────────────────────────────────────────────── フロントページの続き Ｆターム(参考） 4C081 AC08 BB04 BB07 BB08 CA022 CA162 CA212 CA272 CG03 CG04 CG05 CG07 DA03 DC03 DC05 4C167 AA28 BB02 BB03 BB11 BB14 BB20 BB38 BB47 CC08 CC20 CC21 CC22 CC23 FF03 GG02 GG03 GG05 GG06 GG08 GG14 GG21 GG22 GG23 GG24 HH03 HH17 ─────────────────────────────────────────────────── ─── Continued front page F-term (reference) 4C081 AC08 BB04 BB07 BB08 CA022 CA162 CA212 CA272 CG03 CG04 CG05 CG07 DA03 DC03 DC05 4C167 AA28 BB02 BB03 BB11 BB14 BB20 BB38 BB47 CC08 CC20 CC21 CC22 CC23 FF03 GG02 GG03 GG05 GG06 GG08 GG14 GG21 GG22 GG23 GG24 HH03 HH17
Claims (8)
ルク伝達性を備えた芯材であって、上記挿入部と導入部
とを化学組成の異なる線材で構成し、且つ挿入部と導入
部を一体に接合したことを特徴とする医療用ガイドワイ
ヤ用芯材。1. A core material in which the insertion portion has conformability and the introduction portion has torque transmission properties, and the insertion portion and the introduction portion are made of wire rods having different chemical compositions, and A core material for a medical guide wire, wherein the introduction portion is integrally joined.
合金、Ｃｕ−Ａｌ−Ｎｉ系合金またはＦｅ−Ｎｉ−Ｃｏ
−Ｔｉ系合金であり、導入部を構成する線材が、ステン
レス鋼またはＣｏ−Ｎｉ−Ｃｒ−Ｆｅ系合金である請求
項１記載の医療用ガイドワイヤ用芯材。2. The wire material constituting the insert portion is a Ti—Ni based alloy, a Cu—Al—Ni based alloy or a Fe—Ni—Co alloy.
The core material for a medical guide wire according to claim 1, which is a -Ti-based alloy and the wire material constituting the introduction portion is stainless steel or a Co-Ni-Cr-Fe-based alloy.
構成する線材と親和性を有するろう接合金を介して接合
した請求項１または２記載の医療用ガイドワイヤ用芯
材。3. The core material for a medical guide wire according to claim 1 or 2, wherein the insertion portion and the introduction portion are joined via a brazing filler metal having an affinity with the wire material forming each portion.
ｉ箔、またはＢとＳｉを含有し残部がＮｉからなるアモ
ルファス箔である請求項３記載の医療用ガイドワイヤ用
芯材。4. The braze alloy is a silver braze containing B, N.
The core material for a medical guide wire according to claim 3, which is an i foil or an amorphous foil containing B and Si with the balance being Ni.
ドワイヤ。5. A medical guide wire using the core material according to claim 1.
ドワイヤ。6. A medical guide wire using the core material according to claim 2.
ドワイヤ。7. A medical guide wire using the core material according to claim 3.
ドワイヤ。8. A medical guide wire using the core material according to claim 4.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2001361033A JP2003159333A (en) | 2001-11-27 | 2001-11-27 | Core material for guide wire for medical treatment and guide wire for medical treatment |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2001361033A JP2003159333A (en) | 2001-11-27 | 2001-11-27 | Core material for guide wire for medical treatment and guide wire for medical treatment |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JP2003159333A true JP2003159333A (en) | 2003-06-03 |
Family
ID=19171756
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2001361033A Pending JP2003159333A (en) | 2001-11-27 | 2001-11-27 | Core material for guide wire for medical treatment and guide wire for medical treatment |
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| Country | Link |
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| JP (1) | JP2003159333A (en) |
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