JP5432932B2 - Electrode catheter - Google Patents
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- JP5432932B2 JP5432932B2 JP2011018536A JP2011018536A JP5432932B2 JP 5432932 B2 JP5432932 B2 JP 5432932B2 JP 2011018536 A JP2011018536 A JP 2011018536A JP 2011018536 A JP2011018536 A JP 2011018536A JP 5432932 B2 JP5432932 B2 JP 5432932B2
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Description
本発明は、電極カテーテルに関し、特に、心臓の電気生理学的検査において、冠状静脈洞内の電位を測定する際に、冠状静脈洞枝部（大心静脈、左室側壁静脈、左室後側壁静脈）へ容易に挿入することを可能にした電極カテーテルに関する。 The present invention relates to an electrode catheter, and more particularly to coronary sinus branches (large cardiac vein, left ventricular side wall, left ventricular side wall vein) when measuring the potential in the coronary sinus in electrophysiological examination of the heart. The present invention relates to an electrode catheter that can be easily inserted into the catheter.
従来の電極カテーテルとして、ガイドワイヤーを用いたものが提案されている（例えば、特許文献１参照）。 As a conventional electrode catheter, one using a guide wire has been proposed (for example, see Patent Document 1).
これに関連する技術として、特許文献１には、ガイドワイヤーを冠状静脈洞に挿入し、目的の枝部位に留置後、先端ルーメン付電極カテーテルをガイドワイヤーの誘導路を通じてアプローチを行う電極カテーテルが開示されている。 As a technique related to this, Patent Document 1 discloses an electrode catheter in which a guide wire is inserted into a coronary sinus and placed at a target branch site, and then an electrode catheter with a distal lumen is approached through a guide wire guiding path. Has been.
しかし、この特許文献１に記載された従来のルーメン付電極カテーテルは、ガイドワイヤーを通すモノレールルーメンを有するため、先端の外径が少なくともガイドワイヤーの外径にモノレールルーメンの厚みを加えたものより太くなり、冠状静脈洞枝部位等の細径の部位まで到達しづらいという問題がある。 However, since the conventional electrode catheter with a lumen described in Patent Document 1 has a monorail lumen through which a guide wire passes, the outer diameter of the tip is larger than at least the outer diameter of the guide wire plus the thickness of the monorail lumen. Therefore, there is a problem that it is difficult to reach a small-diameter site such as a coronary sinus branch site.
また、電極カテーテルの先端にモノレールルーメンを設けているため、構造が複雑であり、部品点数増となり、製造工程が増加する。また、電極カテーテルとガイドワイヤーは、並列で挿入されるため、血管内の占有割合が増加し、血管への負担が増加する。さらに、ガイドワイヤーと電極カテーテルを順序だてて挿入する必要があるため、手技に時間を要する。 In addition, since the monorail lumen is provided at the tip of the electrode catheter, the structure is complicated, the number of parts increases, and the manufacturing process increases. In addition, since the electrode catheter and the guide wire are inserted in parallel, the occupation ratio in the blood vessel increases and the burden on the blood vessel increases. Furthermore, since it is necessary to insert the guide wire and the electrode catheter in order, the procedure takes time.
従って、本発明の目的は、冠状静脈洞の深部等の細径の部位の電位を測定するとともに、挿入時の患者への負担を軽減する電極カテーテルを提供することにある。 Accordingly, an object of the present invention is to provide an electrode catheter that measures the potential of a small-diameter site such as the deep part of the coronary sinus and reduces the burden on the patient during insertion.
本発明の一態様は、上記目的を達成するため、以下の電極カテーテルを提供する。 In order to achieve the above object, one aspect of the present invention provides the following electrode catheter.
［１］熱可塑性プラスチック組成物からなり可撓性を有するチューブと、
前記チューブの先端部の側面に配置された電極と、
前記チューブの先端に取り付けられ、前記チューブよりも細径であって、円弧状に曲げ加工され、先端が半球状であるガイド部とを備えることを特徴とする電極カテーテル。
[1] A flexible tube made of a thermoplastic composition;
An electrode disposed on a side surface of the distal end of the tube;
An electrode catheter comprising: a guide portion attached to a distal end of the tube, having a smaller diameter than the tube , being bent into an arc shape, and having a hemispherical distal end.
［２］前記ガイド部は、中心に芯材を有する前記［１］に記載の電極カテーテル。
[ 2 ] The electrode catheter according to [ 1 ], wherein the guide portion has a core material in the center.
［３］前記ガイド部の前記芯材は、前記チューブの基端から内腔を経て前記ガイド部の中心に設けられる前記［２］に記載の電極カテーテル。
[ 3 ] The electrode catheter according to [ 2] , wherein the core member of the guide portion is provided at the center of the guide portion through a lumen from a proximal end of the tube.
請求項１に係る発明によれば、冠状静脈洞の深部等の細径の部位の電位を測定することができるとともに、挿入時の患者への負担を軽減することができ、さらに、挿入時の方向性を制御しながら挿入することができ、血管及び内部の組織を傷付けにくくすることができる。
According to the first aspect of the invention, it is possible to measure the potential of a small-diameter portion such as the deep part of the coronary sinus, reduce the burden on the patient at the time of insertion, Insertion can be performed while controlling the directionality, and blood vessels and internal tissues can be made less likely to be damaged .
請求項２に係る発明によれば、ガイド部の曲げ剛性や可撓性を得ることができる。
According to the invention which concerns on Claim 2 , the bending rigidity and flexibility of a guide part can be obtained.
請求項３に係る発明によれば、チューブに曲げ剛性や可撓性がない場合であっても、芯材により曲げ剛性や可撓性を得ることができる。
According to the invention which concerns on Claim 3 , even if it is a case where a tube does not have bending rigidity and flexibility, bending rigidity and flexibility can be obtained with a core material.
（電極カテーテルの構成）
以下、本発明の実施の形態を図面に基づいて説明する。
(Configuration of electrode catheter)
Hereinafter, embodiments of the present invention will be described with reference to the drawings.
図１は、本発明の実施の形態に係る電極カテーテルの構成の一例を示す概略図である。 FIG. 1 is a schematic diagram showing an example of the configuration of an electrode catheter according to an embodiment of the present invention.
電極カテーテル１Ａは、先端部の表面に複数の電極２０を有するチューブ１０と、チューブ１０より細径であるガイド部３０と、コネクタ４０とを備え、コネクタ４０を介して図示しない医療計測機器等に接続された状態で使用されて、例えば心電位等を検出する。 1 A of electrode catheters are provided with the tube 10 which has the some electrode 20 on the surface of the front-end | tip part, the guide part 30 which is diameter smaller than the tube 10, and the connector 40, and it does not show in figure medical measuring instruments etc. via the connector 40 Used in a connected state, for example, detects an electrocardiogram or the like.
チューブ１０は、長さ、太さ、材質等を適宜調節・選択できるが、例えば、内径１．０ｍｍ、外径１．３ｍｍ、長さ約１６００ｍｍで、熱可塑性プラスチック組成物としてショアＤ４０〜７４硬度のポリアミドエラストマー又はポリアミド樹脂を用いることができる。 The length, thickness, material, etc. of the tube 10 can be adjusted and selected as appropriate. For example, the tube 10 has an inner diameter of 1.0 mm, an outer diameter of 1.3 mm, and a length of about 1600 mm. Polyamide elastomer or polyamide resin can be used.
電極２０は、内径１．２５ｍｍ、外径１．３ｍｍ、長さ１ｍｍのプラチナ合金管を用いることができ、チューブ１０の先端部の側面にチューブ１０の長さ方向に５〜２０個、予め定めた間隔で配置される。 As the electrode 20, a platinum alloy tube having an inner diameter of 1.25 mm, an outer diameter of 1.3 mm, and a length of 1 mm can be used, and 5 to 20 pieces in the length direction of the tube 10 are predetermined on the side surface of the distal end portion of the tube 10. Arranged at different intervals.
ガイド部３０は、チューブ１０の先端に、外径０．４ｍｍ、長さ２５ｍｍで、ショアＤ３５〜５５硬度のポリアミドエラストマー樹脂を用いることができる。また、ガイド部３０の先端は、半球状に形成されるとともに、ガイド部３０の先端から８ｍｍの部分はＲ５ｍｍの円弧状に９０°で曲げ加工が施される。また、ガイド部３０の基端は、前記チューブ１０とテーパー形状で接続されており、冠状静脈洞への到達性と細い冠状静脈洞枝部位への選択性を実現している。 For the guide portion 30, a polyamide elastomer resin having an outer diameter of 0.4 mm, a length of 25 mm, and a Shore D35 to 55 hardness can be used at the tip of the tube 10. The tip of the guide portion 30 is formed in a hemispherical shape, and a portion 8 mm from the tip of the guide portion 30 is bent into a circular arc of 5 mm at 90 °. In addition, the proximal end of the guide portion 30 is connected to the tube 10 in a tapered shape to achieve reachability to the coronary sinus and selectivity to a thin coronary sinus branch site.
なお、図１に示す例は、チューブ１０の先端部の側面に電極２０が５〜１２極設けられた場合であり、各電極２０は、チューブ１０の中を通る絶縁リード線７０（図３及び図４参照）に電気的に接続され、絶縁リード線７０を結線してコネクタ４０に接続される。 The example shown in FIG. 1 is a case where 5 to 12 electrodes 20 are provided on the side surface of the distal end portion of the tube 10, and each electrode 20 has an insulating lead wire 70 (see FIGS. 3 and 3) passing through the tube 10. 4) and electrically connected to the connector 40 by connecting the insulated lead wire 70.
図２は、本発明の実施の形態に係る電極カテーテルの構成の他の例を示す概略図である。 FIG. 2 is a schematic view showing another example of the configuration of the electrode catheter according to the embodiment of the present invention.
図２に示す電極カテーテル１Ｂは、チューブ１０の先端部の側面に電極２０が１１〜２０極設けられた場合であり、電極２０の数の増加に従い絶縁リード線７０の本数が増加するため、絶縁リード線７０は分岐コネクタ５０において２本のケーブル５１に分岐され、分岐されたケーブル５１はそれぞれコネクタ４１に接続される。なお、コネクタ４１は、コネクタ４０と同様に医療計測機器の端子へ接続される。 The electrode catheter 1B shown in FIG. 2 is a case where 11 to 20 electrodes 20 are provided on the side surface of the distal end portion of the tube 10, and the number of the insulated lead wires 70 increases as the number of the electrodes 20 increases. The lead wire 70 is branched into two cables 51 at the branch connector 50, and each of the branched cables 51 is connected to the connector 41. In addition, the connector 41 is connected to the terminal of a medical measuring device like the connector 40.
（実施の形態の効果）
上記した実施の形態によると、電極カテーテル１Ａ（１Ｂ）の先端に従来のガイドワイヤーと同等の機能を有するガイド部３０を設けたため、ガイドワイヤーを要することなく電極２０を冠状静脈洞の深部へ到達させることができる。
(Effect of embodiment)
According to the above-described embodiment, since the guide portion 30 having the same function as the conventional guide wire is provided at the distal end of the electrode catheter 1A (1B), the electrode 20 reaches the deep portion of the coronary sinus without requiring a guide wire. Can be made.
また、ガイドワイヤールーメン等を設ける必要がないため、チューブ１０の外径が従来のモノレールルーメン付電極カテーテルの外径に比べて小径となる。また、小経化した本発明の電極カテーテルと同程度の冠状静脈洞の深部への到達を目的とした従来のモノレールルーメン付電極カテーテルを作るには、電極カテーテルを挿入した際の血管内の占有割合を考えたとき、本発明の電極カテーテルの外径に対して従来のモノレールルーメン付電極カテーテルの外径は更に細くする必要があり、結果として電極も小さくなるために心電位を感知しづらくなるという欠点がある。これに対して、本発明の電極カテーテルは電極２０を小型化することなくチューブ１０の先端側の側面に設けることができるので、患部と電極２０との接触面積が広く確保され、医療計測機器において十分な心電位を得ることができる。 Moreover, since it is not necessary to provide a guide wire lumen or the like, the outer diameter of the tube 10 is smaller than the outer diameter of a conventional electrode catheter with a monorail lumen. In addition, in order to make a conventional electrode catheter with a monorail lumen for the purpose of reaching the deep part of the coronary sinus to the same extent as the electrode catheter of the present invention, the occupation in the blood vessel when the electrode catheter is inserted When considering the ratio, it is necessary to further reduce the outer diameter of the conventional electrode catheter with a monorail lumen with respect to the outer diameter of the electrode catheter of the present invention, and as a result, the electrode becomes smaller and it becomes difficult to sense the cardiac potential. There is a drawback. On the other hand, since the electrode catheter of the present invention can be provided on the side surface on the distal end side of the tube 10 without downsizing the electrode 20, a wide contact area between the affected part and the electrode 20 is ensured. Sufficient cardiac potential can be obtained.
また、従来のモノレールルーメン付電極カテーテルの構造と比べてガイド部３０の構造が単純であるため、製造工程が減少し、構成部材の点数も削減できる。 Moreover, since the structure of the guide part 30 is simple compared with the structure of the conventional electrode catheter with a monorail lumen, a manufacturing process reduces and the number of components can also be reduced.
また、従来のモノレールルーメン付電極カテーテルのようにガイドワイヤーと電極カテーテルを順序だてて挿入する必要がないため、挿入時の手順を減少することができる。 Further, since it is not necessary to insert the guide wire and the electrode catheter in order as in the conventional electrode catheter with a monorail lumen, it is possible to reduce the procedure at the time of insertion.
また、ガイド部３０の先端を半球状に加工し、さらに円弧状に曲げ加工した構造としたため、挿入時の方向性を制御しながら挿入することができ、血管及び内部の組織を傷付けにくくすることができる。 In addition, since the tip of the guide portion 30 is processed into a hemispherical shape and further bent into an arc shape, the guide portion 30 can be inserted while controlling the directionality at the time of insertion, thereby making it difficult to damage blood vessels and internal tissues. Can do.
図３（ａ）及び（ｂ）は、ガイド部を備えたチューブの先端部の構成の他の例を示す断面図である。本実施例１では、上記した実施の形態のガイド部３０に換えて芯材６０を含むガイド部３１を用いる。 FIGS. 3A and 3B are cross-sectional views showing another example of the configuration of the distal end portion of the tube provided with the guide portion. In the present Example 1, the guide part 31 including the core member 60 is used instead of the guide part 30 of the above-described embodiment.
ガイド部３１は、内部には曲げ剛性が高く、高強度の金属体からなる芯材６０を有する。チューブ１０の直径が１ｍｍ以下の細径等であって曲げ剛性や可撓性を得ることができない場合、芯材６０は、ガイド部３１の内部からチューブ１０の内腔を介し、チューブ１０の基端で固定されることで曲げ剛性や可撓性を得るための役割を兼ねる。なお、チューブ１０が十分な曲げ剛性や可撓性を有する場合は、ガイド部３１のみに芯材６０を設けても良い。 The guide portion 31 has a core member 60 made of a high-strength metal body with high bending rigidity. When the diameter of the tube 10 is a small diameter of 1 mm or less and the bending rigidity and flexibility cannot be obtained, the core member 60 is formed from the inside of the guide portion 31 through the lumen of the tube 10 to the base of the tube 10. It also serves to obtain bending rigidity and flexibility by being fixed at the end. Note that when the tube 10 has sufficient bending rigidity and flexibility, the core member 60 may be provided only in the guide portion 31.
ガイド部３１の先端は、上記した実施の形態と同様に半球状に形成されるとともに、ガイド部の先端から８ｍｍの部分はＲ５ｍｍの円弧状に９０°で曲げ加工が施される。 The tip of the guide portion 31 is formed in a hemispherical shape as in the above-described embodiment, and a portion 8 mm from the tip of the guide portion is bent into a circular arc of 5 mm at 90 °.
芯材６０は、例えば、ニッケル・チタン合金又はステンレス鋼等の直径０．３４ｍｍの芯材であり、ガイド部３１の柔軟性を得るため、図３（ｂ）に示すように、先端を直径０．０６ｍｍまで細径化したテーパー形状とする。 The core material 60 is a core material having a diameter of 0.34 mm, such as nickel / titanium alloy or stainless steel, and has a diameter of 0 mm as shown in FIG. A tapered shape with a diameter reduced to 0.06 mm.
図４は、ガイド部を備えたチューブの先端部の構成の他の例を示す断面図である。本実施例２では、上記した実施例１ガイド部３１に換えて芯材を含まないガイド部３２を用いる。 FIG. 4 is a cross-sectional view showing another example of the configuration of the distal end portion of the tube provided with the guide portion. In the second embodiment, a guide portion 32 that does not include a core material is used instead of the above-described first embodiment guide portion 31.
芯材６０を設けないガイド部３２は、ショア硬度４０Ｄのポリアミドエラストマーにて形成され、チューブ１０とテーパー形状で接続される。ガイド部３２の先端は半球状に形成されるとともに、ガイド部の先端から８ｍｍの部分はＲ５ｍｍの円弧状に９０°で曲げ加工が施される。 The guide portion 32 not provided with the core member 60 is formed of a polyamide elastomer having a Shore hardness of 40D and is connected to the tube 10 in a tapered shape. The tip of the guide portion 32 is formed in a hemispherical shape, and a portion 8 mm from the tip of the guide portion is bent into an arc of R5 mm at 90 °.
芯材６０を使用せず前記ガイド部３２を形成したため、実施例１に比べて部品点数を削減でき、安価に作製することができる。 Since the guide portion 32 is formed without using the core member 60, the number of parts can be reduced as compared with the first embodiment, and the guide portion 32 can be manufactured at a low cost.
［他の実施の形態］
なお、本発明は、上記実施の形態に限定されず、本発明の趣旨を逸脱しない範囲で種々な変形が可能である。
[Other embodiments]
The present invention is not limited to the above embodiment, and various modifications can be made without departing from the spirit of the present invention.
１Ａ 電極カテーテル
１Ｂ 電極カテーテル
１０ チューブ
２０ 電極
３０−３２ ガイド部
４０ コネクタ
４１ コネクタ
５０ 分岐コネクタ
５１ ケーブル
６０ 芯材
７０ 絶縁リード線
DESCRIPTION OF SYMBOLS 1A Electrode catheter 1B Electrode catheter 10 Tube 20 Electrode 30-32 Guide part 40 Connector 41 Connector 50 Branch connector 51 Cable 60 Core material 70 Insulation lead wire
Claims (3)
前記チューブの先端部の側面に配置された電極と、
前記チューブの先端に取り付けられ、前記チューブよりも細径であって、円弧状に曲げ加工され、先端が半球状であるガイド部とを備えることを特徴とする電極カテーテル。 A flexible tube made of a thermoplastic composition;
An electrode disposed on a side surface of the distal end of the tube;
An electrode catheter comprising: a guide portion attached to a distal end of the tube, having a smaller diameter than the tube , being bent into an arc shape, and having a hemispherical distal end.
The electrode catheter according to claim 2 , wherein the core member of the guide portion is provided at the center of the guide portion through a lumen from a proximal end of the tube.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2011018536A JP5432932B2 (en) | 2011-01-31 | 2011-01-31 | Electrode catheter |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2011018536A JP5432932B2 (en) | 2011-01-31 | 2011-01-31 | Electrode catheter |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JP2012157479A JP2012157479A (en) | 2012-08-23 |
| JP5432932B2 true JP5432932B2 (en) | 2014-03-05 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2011018536A Expired - Fee Related JP5432932B2 (en) | 2011-01-31 | 2011-01-31 | Electrode catheter |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS50103194A (en) * | 1974-01-21 | 1975-08-14 | ||
| JP4850697B2 (en) * | 2003-05-02 | 2012-01-11 | ボストン サイエンティフィック リミテッド | Multi-function medical catheter |
| JP4305042B2 (en) * | 2003-05-12 | 2009-07-29 | ニプロ株式会社 | Artificial insemination catheter device |
| JP2005058326A (en) * | 2003-08-08 | 2005-03-10 | Sumitomo Bakelite Co Ltd | Nasal cavity guide tube |
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| JP2012157479A (en) | 2012-08-23 |
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