WO2017145503A1 - 電極カテーテル - Google Patents
電極カテーテル Download PDFInfo
- Publication number
- WO2017145503A1 WO2017145503A1 PCT/JP2016/087523 JP2016087523W WO2017145503A1 WO 2017145503 A1 WO2017145503 A1 WO 2017145503A1 JP 2016087523 W JP2016087523 W JP 2016087523W WO 2017145503 A1 WO2017145503 A1 WO 2017145503A1
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- WIPO (PCT)
- Prior art keywords
- catheter shaft
- tube
- lumen
- catheter
- electrode
- Prior art date
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/271—Arrangements of electrodes with cords, cables or leads, e.g. single leads or patient cord assemblies
- A61B5/273—Connection of cords, cables or leads to electrodes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/283—Invasive
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/271—Arrangements of electrodes with cords, cables or leads, e.g. single leads or patient cord assemblies
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/283—Invasive
- A61B5/287—Holders for multiple electrodes, e.g. electrode catheters for electrophysiological study [EPS]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
- A61B5/6852—Catheters
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6867—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive specially adapted to be attached or implanted in a specific body part
- A61B5/6869—Heart
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
- A61M25/0012—Making of catheters or other medical or surgical tubes with embedded structures, e.g. coils, braids, meshes, strands or radiopaque coils
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0054—Catheters; Hollow probes characterised by structural features with regions for increasing flexibility
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0133—Tip steering devices
- A61M25/0147—Tip steering devices with movable mechanical means, e.g. pull wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
- A61B2017/00292—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery mounted on or guided by flexible, e.g. catheter-like, means
- A61B2017/003—Steerable
- A61B2017/00318—Steering mechanisms
- A61B2017/00323—Cables or rods
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/12—Manufacturing methods specially adapted for producing sensors for in-vivo measurements
- A61B2562/125—Manufacturing methods specially adapted for producing sensors for in-vivo measurements characterised by the manufacture of electrodes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M2025/0004—Catheters; Hollow probes having two or more concentrically arranged tubes for forming a concentric catheter system
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0021—Catheters; Hollow probes characterised by the form of the tubing
- A61M25/0023—Catheters; Hollow probes characterised by the form of the tubing by the form of the lumen, e.g. cross-section, variable diameter
- A61M25/0026—Multi-lumen catheters with stationary elements
- A61M2025/0039—Multi-lumen catheters with stationary elements characterized by lumina being arranged coaxially
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M2025/018—Catheters having a lateral opening for guiding elongated means lateral to the catheter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0133—Tip steering devices
- A61M25/0136—Handles therefor
Definitions
- the present invention relates to an electrode catheter, and more particularly to an electrode catheter provided with a catheter shaft composed of a blade tube.
- a catheter shaft constituting an electrode catheter such as an EP catheter is provided with a plurality of ring electrodes on the outer peripheral surface of the distal end portion thereof.
- Conductive wires connected to the plurality of ring electrodes respectively enter the lumen of the catheter shaft from the side holes formed in the tube wall of the shaft corresponding to the mounting positions of the ring electrodes and extend to the lumen.
- the proximal ends of the conducting wires are respectively connected to terminals arranged inside the connector connected to the proximal end side of the catheter shaft.
- an electrode catheter in which a proximal end portion of a catheter shaft is configured by a resin tube (blade tube) reinforced by a braid made of metal such as stainless steel (see, for example, Patent Document 1 below).
- a resin tube blade tube
- a braid made of metal such as stainless steel
- an electrode catheter including a catheter shaft having a proximal end portion constituted by a blade tube is not sufficient in torque transmission, and further improvement is desired.
- a large-diameter central lumen is formed as a guide wire lumen on the catheter shaft that constitutes the electrode catheter. Since the ratio of the resin constituting the shaft is low) and sufficient torque transmission cannot be exhibited, improvement of torque transmission in an electrode catheter having a guide wire lumen is an important issue.
- the metal wire constituting the braid is exposed on the inner peripheral surface of the side hole. Therefore, the conductor of the ring-shaped electrode is used when the electrode catheter is manufactured and used. It is conceivable that the resin coating layer constituting the conducting wire is damaged and the insulation of the conducting wire is impaired.
- An object of the present invention is to provide excellent torque transmission as compared with a conventionally known electrode catheter in which a proximal end portion of a catheter shaft is constituted by a blade tube reinforced by a metal braid, and a tube at the distal end portion of the catheter shaft. It is easy to form a side hole through which the conducting wire of the ring electrode passes through the wall, and the resin coating layer of the conducting wire inserted into the formed side hole constitutes a braid that is exposed on the inner peripheral surface of the side hole.
- An object of the present invention is to provide an electrode catheter that is not damaged by a wire.
- Another object of the present invention is to provide an electrode catheter excellent in torque transmission provided with a catheter shaft having a guide wire lumen.
- An electrode catheter of the present invention includes a catheter shaft having at least one lumen, at least one ring-shaped electrode mounted on the outer peripheral surface of the distal end portion of the catheter shaft, and a conductive wire connected to the ring-shaped electrode. And A side hole from the outer peripheral surface to the lumen is formed in the tube wall of the distal end portion of the catheter shaft corresponding to the mounting position of the ring-shaped electrode, The conductive wire is formed by coating a metal core wire with resin, and is connected to the ring-shaped electrode by being joined to the inner peripheral surface of the ring-shaped electrode at a tip portion thereof, and enters the lumen from the side hole.
- the catheter shaft is a blade tube reinforced by a braid over its entire length, and the braid that reinforces at least the distal end portion of the catheter shaft is constituted by a resin-made blade tube. .
- the catheter shaft is formed of the blade tube over the entire length including the distal end portion, it is possible to exhibit excellent torque transmission.
- the braid that reinforces the distal end portion of the catheter shaft is made of resin, a side hole for easily passing the lead wire of the ring electrode is easily formed in the tube wall of the distal end portion can do. Further, depending on the resin wire exposed on the inner peripheral surface of the side hole, the resin coating layer of the conducting wire inserted through the side hole is not damaged. Further, since the braid is also embedded in the distal end portion of the catheter shaft, the shapeability at the distal end portion is improved.
- the catheter shaft is constituted by the blade tube reinforced by a resin braid over its entire length.
- the catheter shaft is formed of the blade tube over the entire length including the distal end portion, it is possible to exhibit excellent torque transmission.
- the blade tube constituting the catheter shaft is a resin tube reinforced by a resin braid, and all is made of a resin material. Therefore, a side hole for passing the lead wire of the ring electrode through the tube wall of the distal end portion is formed. It can be formed easily. Further, depending on the resin wire exposed on the inner peripheral surface of the side hole, the resin coating layer of the conducting wire inserted through the side hole is not damaged. Further, since the braid is also embedded in the distal end portion of the catheter shaft, the shapeability at the distal end portion is improved.
- the blade tube reinforced by the resin braid over the entire length of the catheter shaft can be manufactured by one extrusion molding, for example, by the tip portion reinforced by the resin braid and the metal braid. Manufacture is easy as compared with a blade tube formed by joining a reinforced base end portion. Further, the kink that is likely to occur at the shaft portion where the constituent material of the braid is switched does not occur.
- the catheter shaft may be constituted by the blade tube having a distal end portion reinforced by a resin braid and a proximal end portion reinforced by a metal braid. Good.
- the catheter shaft is formed of the blade tube over the entire length including the distal end portion, it is possible to exhibit excellent torque transmission.
- the braid that reinforces the tip of the blade tube that constitutes the catheter shaft is made of resin, a side hole is easily formed in the tube wall of the tip of the catheter shaft to pass the lead wire of the ring electrode. can do. Further, depending on the resin wire exposed on the inner peripheral surface of the side hole, the resin coating layer of the conducting wire inserted through the side hole is not damaged. Further, since the braid is also embedded in the distal end portion of the catheter shaft, the shapeability at the distal end portion is improved.
- the catheter shaft has a guide wire lumen. It is effective to employ the configuration of the present invention when the catheter shaft has a guide wire lumen as in the electrode catheter having such a configuration and the ratio of the resin constituting the shaft is low.
- the catheter shaft includes an inner tube having a guide wire lumen, and an outer tube that forms a lumen for inserting the conductive wire together with an outer peripheral surface of the inner tube.
- the outer tube is preferably the blade tube.
- the electrode catheter having such a configuration it is possible to exhibit excellent torque transmission as is apparent from the results of Examples described later, even though the ratio of the resin constituting the catheter shaft is low. .
- the catheter shaft is preferably a multi-lumen tube having a plurality of lumens inside the braid.
- the electrode catheter of the present invention it is possible to exhibit torque transmission superior to a conventionally known electrode catheter in which the proximal end portion of the catheter shaft is configured by a blade tube reinforced by a metal braid. Further, the side hole for passing the lead wire of the ring-shaped electrode can be easily processed in the tube wall at the distal end portion of the catheter shaft, and the resin coating layer of the lead wire inserted into the formed side hole has the side hole. It is not damaged by the resin wire exposed on the inner peripheral surface of the wire. Moreover, even if the electrode catheter of the present invention includes a catheter shaft having a guide wire lumen, the electrode catheter is excellent in torque transmission.
- FIG. 3 is a transverse sectional view (IIIA-IIIA sectional view) of the catheter shaft shown in FIG.
- FIG. 3 is a transverse sectional view (IIIB-IIIB sectional view) of the catheter shaft shown in FIG. 2.
- FIG. 3 is a transverse sectional view (IIIC-IIIC sectional view) of the catheter shaft shown in FIG. 2.
- the electrode catheter shown in FIG. 1 it is sectional drawing which shows typically the state in which the conducting wire of a ring-shaped electrode has penetrated the lumen of the catheter shaft through the side hole.
- FIG. 7 is a transverse sectional view (VIIA-VIIA sectional view) of a catheter shaft that constitutes the electrode catheter shown in FIG. 6.
- FIG. 7 is a transverse sectional view (VIIB-VIIB sectional view) of a catheter shaft constituting the electrode catheter shown in FIG. 6; It is a graph which shows the result of an evaluation test of torque transmission nature about an electrode catheter by an example and a comparative example. It is a side view which shows the electrode catheter which concerns on 3rd Embodiment of this invention.
- FIG. 7 is a transverse sectional view (VIIA-VIIA sectional view) of a catheter shaft that constitutes the electrode catheter shown in FIG. 6.
- FIG. 7 is a transverse sectional view (VIIB-VIIB sectional view) of a catheter shaft constituting the electrode catheter shown in FIG. 6; It is a graph which shows the result of an evaluation test of torque transmission nature about an electrode catheter by an example and a comparative example.
- It is
- FIG. 10 is a side view showing a catheter shaft constituting the electrode catheter shown in FIG. 9.
- FIG. 11 is a transverse sectional view (XIA-XIA sectional view) of the catheter shaft shown in FIG. 10.
- FIG. 11 is a transverse sectional view (XIB-XIB sectional view) of the catheter shaft shown in FIG. 10.
- FIG. 11 is a transverse sectional view (XIC-XIC sectional view) of the catheter shaft shown in FIG. 10.
- FIG. 10 is a cross-sectional view schematically showing a state where the lead wire of the ring-shaped electrode enters the lumen of the catheter shaft through the side hole in the electrode catheter shown in FIG. 9.
- the electrode catheter 100 of this embodiment shown in FIGS. 1 to 5 is used for measuring the potential of a site such as a coronary artery of the heart.
- the electrode catheter 100 includes a catheter shaft 10, ring-shaped electrodes 201 to 210 attached to the outer peripheral surface of the distal end portion 101 of the catheter shaft 10, and lead wires 301 to 310 connected to the ring-shaped electrodes 201 to 210, respectively.
- the catheter shaft 10 includes an inner tube 11 having a guide wire lumen 11L, and an outer tube 13 that forms a lumen 12L for inserting the conducting wires 301 to 310 together with the outer peripheral surface of the inner tube 11,
- the outer tube 13 is composed of a blade tube reinforced by a braid 135 made of resin over its entire length, and the side wall 15 extending from the outer peripheral surface to the lumen 12L is formed in the tube wall of the outer tube 13 at the distal end portion 101 of the catheter shaft 10.
- the conductive wires 301 to 310 are formed corresponding to the mounting positions, and the leading ends thereof are connected to the inner peripheral surfaces of the ring electrodes 201 to 210 to be connected to the ring electrodes 201 to 210, and It enters the lumen 12L from the side hole 15 and extends to the lumen 12L.
- 25 is a distal tip attached to the distal end side of the catheter shaft 10
- 40 is a handle connected to the proximal end side of the catheter shaft 10
- 41 is a proximal end portion of each of the conducting wires 301 to 310.
- the guide wire protection tube has a single lumen structure that includes the inner tube 11 extending from the handle 40 toward the guide wire port 42.
- the catheter shaft 10 constituting the electrode catheter 100 is a double tube structure shaft constituted by an inner tube 11 and an outer tube 13.
- the catheter shaft 10 includes a distal end portion 101 and a proximal end portion 102, and the distal end portion 101 includes a distal end side low hardness region 101A and a hardness inclined region 101B. As shown in FIG. 1, the distal end portion 101 of the catheter shaft 10 has a specific curve shape. In FIG. 2, the tip portion 101 having a curved shape is illustrated linearly.
- the tip portion 101 having a specific curve shape (stored) is easily deformed by applying an external force (for example, by inserting the catheter shaft 10 through the tube), but when the external force is removed, the stored curve is stored. The shape can be restored.
- the effective length (L1) of the catheter shaft 10 is usually 400 to 1500 mm, and 650 mm if a suitable example is shown. Further, the length (L2) of the tip portion 101 is usually 50 to 200 mm, and 95 mm if a suitable example is shown. Further, the length (L3) of the tip side low hardness region 101A of the tip portion 101 is usually 20 to 100 mm, and is 45 mm if a suitable example is shown. Further, the length (L4) of the hardness gradient region 101B of the tip portion 101 is usually 20 to 100 mm, and is 50 mm if a suitable example is shown.
- the inner tube 11 constituting the catheter shaft 10 is a single lumen tube having a two-layer structure including an inner layer 111 and an outer layer 112, and a guide wire lumen 11 ⁇ / b> L is formed by the inner tube 11.
- high-density polyethylene or the like can be used as a constituent material of the inner layer 111.
- polyether block amide (PEBAX) or the like as a constituent material of the outer layer 112, polyether block amide (PEBAX) or the like can be used as a constituent material of the outer layer 112.
- the inner diameter of the inner tube 11 is usually 0.5 to 1.5 mm, and 1.0 mm is shown as a suitable example.
- the outer diameter of the inner tube 11 is normally 0.6 to 1.7 mm, and 1.2 mm if a suitable example is shown.
- the outer tube 13 constituting the catheter shaft 10 is a blade tube which is a resin tube reinforced by a resin braid 135.
- a resin braid 135 as a reinforcing material is embedded in the outer tube 13 over the entire length of the catheter shaft 10 (the distal end portion 101 and the proximal end portion 102).
- the outer tube 13 is a single-lumen tube having a three-layer structure including an inner layer 131, a reinforcing layer 133 formed of a braid 135, and an outer layer 132.
- the inner peripheral surface of the outer tube 13 A lumen 12 ⁇ / b> L is formed by the outer peripheral surface of the inner tube 11.
- the constituent material of the inner layer 131 of the outer tube 13 As a constituent material (inner surface resin) of the inner layer 131 of the outer tube 13, a synthetic resin such as polyolefin, polyamide, polyether polyamide, polyurethane, nylon, polyether block amide (PEBAX) can be used. It is preferred to use PEBAX.
- the constituent material of the inner layer 131 has the same hardness over the entire length of the catheter shaft 10.
- the hardness of the constituent material of the inner layer 131 is, for example, 72D.
- the wall thickness of the inner layer 131 is usually 10 to 50 ⁇ m, and 25 ⁇ m is shown as a suitable example.
- the constituent material (outer surface resin) of the outer layer 132 of the outer tube 13 the same kind of resin as that of the inner layer 131 can be used, and among these, it is preferable to use PEBAX.
- the constituent material of the outer layer 132 has different hardness along the length direction of the catheter shaft 10.
- the hardness of the outer layer 132 (132a) constituting the distal-side low hardness region 101A of the distal end portion 101 is 35D
- the hardness of the outer layer 132 (132c) constituting the proximal end portion 102 is 72D.
- the hardness of the outer layer 132 (132b) constituting the hardness gradient region 101B of the tip portion 101 changes (decreases) in an inclined manner from 72D to 35D in the tip direction.
- the thickness of the outer layer 132 is usually 30 to 200 ⁇ m, and is 95 ⁇ m if a suitable example is shown.
- the reinforcing layer 133 of the outer tube 13 includes a resin braid 135 and a resin 134 filled in a gap between the resin wires constituting the braid 135.
- the braid 135 includes 16 sets (32 pieces) of resin wires arranged at equal angular intervals in the circumferential direction.
- the resin 134 constituting the reinforcing layer 133 is a resin in which a part of the constituent material of the outer layer 132 is melted and filled into the gap between the resin wires when the outer tube 13 is manufactured.
- the constituent material of the braid 135 is selected from resins that can exhibit a reinforcing effect when embedded.
- the hardness of the constituent material of the braid 135 is preferably 72D or more. When this hardness is too small, there may be a case where a sufficient reinforcing effect and thus good torque transmission cannot be exhibited.
- the bending elastic modulus (ISO178 or JIS K7171) of the constituent material of the braid 135 is usually 500 to 19,000 MPa, preferably 2,000 to 7,000 MPa, more preferably 3,500 to 4,200. If a suitable example is shown, it is set to 4,200 MPa.
- the melting point of the constituent material of the braid 135 is preferably higher than the melting point of the constituent materials of the inner layer 131 and the outer layer 132 so that the structure of the braid can be maintained under heating conditions when manufacturing the blade tube.
- PEEK resin polyimide resin, polyamide resin, polyester resin and the like can be cited as suitable reinforcing resins constituting the braid 135 (resin wire), and among these, PEEK resin is particularly preferable.
- the wire diameter of the resin wire constituting the braid 135 is usually 30 to 100 ⁇ m, and 60 ⁇ m if a suitable example is shown. Further, the number of strikes of the braid 135 is normally 8 to 32, and is 16 if a suitable example is shown. Further, the number of braids 135 is normally 1 to 4, and is 2 if a suitable example is shown.
- the thickness of the reinforcing layer 133 is usually 60 to 200 ⁇ m, and 120 ⁇ m is shown as a suitable example.
- the inner diameter of the outer tube 13 is usually 0.7 to 2.0 mm, and is 1.5 mm as a suitable example.
- the outer diameter of the outer tube 13 is normally 1.3 to 3.0 mm, and is 2.0 mm as a suitable example.
- the outer tube 13 which is a blade tube, has a braid 135 disposed on the outer peripheral surface of a tubular inner layer forming material, and an outer layer forming material disposed on the outer peripheral surface of the braid 135.
- the ring-shaped electrodes 201 to 210 constituting the electrode catheter 100 are mounted on the outer peripheral surface of the distal end portion 101 (the distal end side low hardness region 101A and the hardness inclined region 101B) of the catheter shaft 10. ing. Lead ends of the conducting wires 301 to 310 are joined to the inner peripheral surfaces of the ring electrodes 201 to 210, respectively.
- a metal having good electrical conductivity such as platinum, gold, silver, aluminum, copper, and stainless steel can be used. From the viewpoint of improving the contrast properties for X-rays, platinum, gold, silver, and alloys containing these as main components are preferable.
- the width of the ring electrodes 201 to 210 (the length in the axial direction of the catheter shaft 10) is, for example, 0.5 to 10 mm. Further, the distance between the electrodes of the ring-shaped electrodes 201 to 210 is, for example, 1 to 10 mm.
- the conducting wire 301 whose tip is joined to the inner peripheral surface of the ring-shaped electrode 201 enters the lumen 12 ⁇ / b> L from the side hole 15 formed in the tube wall of the outer tube 13. Extend 12L.
- 311 is a metal core wire of the conducting wire 301
- 312 is a resin coating layer
- W is a joint.
- a resin wire (not shown) constituting the braid 135 is exposed on the inner peripheral surface of the side hole 15. The same applies to the conducting wires 302 to 310 joined to the inner peripheral surfaces of the ring electrodes 202 to 210.
- a distal tip 25 is connected to the distal end side of the catheter shaft 10. As shown in FIG. 5, a through hole 26 is formed in the distal tip 25, and the distal end portion of the inner tube 11 is inserted into the through hole 26. By inserting the inner tube 11 to which the distal tip 25 is connected in this way into the outer tube 13, the catheter shaft 10 having a double tube structure is configured.
- the proximal end portion of the catheter shaft 10 is inserted into the handle 40 (insertion passage).
- the insertion path of the catheter shaft 10 inside the handle 40 is bifurcated in two directions.
- the conducting wires 301 to 310 extending to the lumen 12L of the catheter shaft 10 are respectively connected to the outer tube 13.
- Each of the proximal ends of the conductors 301 to 310 extends from the proximal end, extends along one branch path, extends from the handle 40, passes through the lumen of the conductor protection tube 51, and is inserted into the connector 41.
- the ring-shaped electrodes 201 to 210 are electrically connected to the terminals in the connector 41, respectively.
- the inner tube 11 constituting the catheter shaft 10 extends from the proximal end of the outer tube 13, extends along the other branch path, extends from the handle 40, and extends from the guide wire protection tube 52. It is connected to the guide wire port 42 through the lumen. Thereby, the guide wire inserted from the guide wire port 42 can be extended from the distal end opening of the distal end tip 25 via the guide wire lumen 11L of the inner tube 11.
- the resin constituting the catheter shaft 10 is made of resin.
- the ratio is low (the ratio of the space is high due to the presence of the guide wire lumen 11L, etc.), it is possible to exhibit excellent torque transmission as is apparent from the results of Examples described later.
- the braid 135 that reinforces the outer tube 13 that is a blade tube is formed of a resin wire, and therefore, the outer tube 13 is made of only a resin material.
- the side hole 15 for passing the conducting wire of the ring electrode can be easily formed.
- the resin wire constituting the braid 135 is inevitably exposed on the inner peripheral surface of the side hole 15, but unlike the case where the metal wire is exposed, the resin wire makes the side hole 15 The resin coating layer of the inserted lead is not damaged.
- the catheter shaft 10 Since the braid 135 is embedded in the outer tube 13 in the distal end portion 101, the distal end portion 101 can easily be bent, so that good shaping properties can be exhibited.
- FIG. 6 is a side view showing an electrode catheter according to a second embodiment of the present invention
- FIGS. 7A and 7B are cross-sectional views of a catheter shaft constituting the electrode catheter, respectively.
- the electrode catheter 200 of this embodiment has a distal end flexible portion 601, a multi-lumen structure catheter shaft 60 in which lumens 61L to 64L are formed, and a distal end electrode 71 connected to the distal end side of the catheter shaft 60.
- the ring-shaped electrodes 72 to 74 attached to the outer peripheral surface of the distal end flexible portion 601 of the catheter shaft 60, the conductive wire 81 connected to the distal electrode 71, and the conductive wire 82 connected to each of the ring-shaped electrodes 72 to 74.
- a first operation wire 86 whose proximal end can be pulled to bend the distal flexible portion 601 of the catheter shaft 60 in the first direction (the direction indicated by arrow A in FIG.
- An operation wire 87 and a control handle 90 attached to the proximal end side of the catheter shaft 60 are provided.
- a side hole extending from the outer peripheral surface to the lumen 62L is formed in the tube wall of the distal end flexible portion 601 of the catheter shaft 60.
- the lead wires 81 to 84 are formed corresponding to the mounting positions of the ring electrodes 72 to 74, the metal core wires are resin-coated, the lead wires 81 of the tip electrode 71 extend to the lumen 61L, and the ring electrodes 72 to 74 are formed.
- the lead wires 82 to 84 are connected to the ring-shaped electrodes 72 to 74 by joining their tip portions to the inner peripheral surfaces of the ring-shaped electrodes 72 to 74, and enter the lumen 62L from the side holes.
- the first operation wire 86 is fixed to the tip electrode 71 and extends to the lumen 63L
- the second operation wire 86 extends to the lumen 62L.
- 87 is made to extend in the lumen 64L with its front end portion is fixed to the tip electrode 71, the catheter shaft 60 is formed of a blade tube reinforced with braided 65 made of resin over its entire length.
- reference numeral 95 denotes a knob for performing a swinging operation (catheter tip deflection operation) of the catheter shaft 60.
- 7A and 7B 67 is an inner (core) portion made of resin constituting the catheter shaft 60, and 69 is an outer (shell) portion made of resin that covers the inner 67.
- the electrode catheter 200 includes a catheter shaft 60, a distal electrode 71 fixed to the distal end thereof, ring-shaped electrodes 72 to 74 attached to the distal flexible portion of the catheter shaft 60, and a catheter shaft. 60 and a control handle 90 mounted on the proximal end side.
- the distal end portion of the hemorrhoid catheter shaft 60 is a distal flexible portion 601.
- the “tip flexible portion” refers to a tip portion of the catheter shaft that can be bent (bent) by pulling the operation wire (the first operation wire 86 or the second operation wire 87).
- the outer diameter of the catheter shaft 60 is usually 0.6 to 3 mm, preferably 1.3 to 2.4 mm.
- the length of the catheter shaft 60 is usually 400 to 1500 mm, preferably 700 to 1200 mm.
- the length of the distal end flexible portion 601 is, for example, 30 to 300 mm, and preferably 50 to 250 mm.
- a control handle 90 is attached to the proximal end side of the catheter shaft 60.
- a connector having a plurality of terminals is provided in the control handle 90, and the terminals of the connector include base end portions of conducting wires 81 and 82 to 84 connected to the tip electrode 71 and the ring electrodes 72 to 74, respectively. Is connected.
- the control handle 90 is equipped with a knob 95 for performing an operation of bending the distal end flexible portion 601 of the catheter shaft 60.
- the catheter shaft 60 is embedded in the inner portion 67 made of resin, the outer portion 69 made of resin covering the inner portion 67, and the outer portion 69 over the entire length of the catheter shaft 60. And a multi-lumen blade tube having four lumens 61L to 64L inside the braid 65 (inner portion 67).
- Examples of the resin constituting the inner portion 67 include thermoplastic polyamide-based elastomers, and polyether block amide (PEBAX) is particularly preferable.
- the hardness of the resin constituting the inner portion 67 is, for example, 25D to 40D.
- the first operation wire 86 and the second operation wire 87 are inserted through the relatively small-diameter lumen 63L and the lumen 64L, which are opposed to each other across the central axis of the catheter shaft 60, respectively.
- the lumen 61L and the lumen 62L are relatively large-diameter lumens arranged to face each other across the central axis of the catheter shaft 60.
- a conducting wire 81 connected to the tip electrode 71 is inserted into the lumen 61L, and conducting wires 82 to 84 connected to the ring electrodes 72 to 74 are inserted into the lumen 62L.
- the lead wire 81 is connected to the tip electrode 71 by the tip portion being connected and fixed to the tip electrode 71 by solder filled in the internal space of the tip electrode 71.
- the conducting wires 82 to 84 are connected to the ring-shaped electrodes 72 to 74 by joining the respective distal end portions thereof to the inner peripheral surfaces of the ring-shaped electrodes 72 to 74, and the distal flexible portion 601 of the catheter shaft 60. It enters the lumen 62L from the side hole formed in the tube wall and is inserted through the lumen 62L.
- the outer portion 69 is made of a resin material that covers the inner portion 67.
- the resin material constituting the outer portion 69 include thermoplastic polyamide-based elastomers, and polyether block amide (PEBAX) is particularly preferable.
- the outer portion 69 may be composed of tubes having the same physical properties along the axial direction, it is preferable that the hardness is changed (decreased) in a slanting or stepwise manner toward the distal end direction.
- the outer portion 69 (69a) shown in FIG. 7A has a hardness of, for example, 25D to 55D
- the outer portion 69 (69b) shown in FIG. 7B has a hardness of 55D to 72D.
- a resin braid 65 that is a reinforcing material is embedded in the outer portion 69.
- the braid 65 includes 16 sets (32 pieces) of resin wire rods arranged at equiangular intervals in the circumferential direction.
- the constituent material of the braid 65 (resin wire), the hardness of the constituent material, the wire diameter of the resin wire, and the like are the same as those of the braid 135 in the electrode catheter 100 of the first embodiment.
- the electrode catheter 200 of the present embodiment includes a first operation wire 86 for bending the distal flexible portion 601 of the catheter shaft 60 in the first direction (the direction indicated by arrow A), and the distal flexible portion of the catheter shaft 60.
- a second operation wire 87 for bending 601 in the second direction (direction indicated by arrow B) is provided.
- the first operation wire 86 is inserted inside the catheter shaft 60 (lumen 63L) so as to be movable in the tube axis direction.
- the distal end of the first operation wire 86 is connected and fixed to the distal electrode 71 by solder filled in the internal space of the distal electrode 71. Further, the proximal end of the first operation wire 86 is connected to a knob 95 of the control handle 90 so that it can be pulled.
- the second operation wire 87 is inserted inside the catheter shaft 60 (lumen 64L) so as to be movable in the tube axis direction.
- the tip of the second operation wire 87 is connected and fixed to the tip electrode 71 by solder, like the first operation wire 86. Further, the proximal end of the second operation wire 87 can be pulled by being connected to a knob 95 of the control handle 90.
- the first operation wire 86 is pulled and moved to the proximal end side of the lumen 63L, and the distal end flexible portion 601 is moved. It can be bent in the first direction (direction indicated by arrow A).
- the second operation wire 87 is pulled and moved to the proximal end side of the lumen 64L, and the distal end flexible portion 601 is moved in the second direction ( Can be bent in the direction indicated by arrow B).
- the braid of the resin braid 65 is embedded in the outer portion 69 over the entire length of the catheter shaft 60, excellent torque transmission can be exhibited.
- the braid 65 that reinforces the catheter shaft 60 is formed of a resin wire, and therefore the catheter shaft 60 is made of only a resin material.
- the side holes for passing the 74 conducting wires 82 to 84 can be easily formed.
- the resin coating layer of the conductive wires 82 to 84 inserted through the side hole is not damaged.
- the electrode catheter 500 of this embodiment shown in FIGS. 9 to 12 is used for measuring the potential of a site such as a coronary artery of the heart.
- the portions denoted by the same reference numerals as those in FIGS. 1 to 4 have the same configuration as the electrode catheter of the first embodiment.
- the electrode catheter 500 of this embodiment includes a catheter shaft 50, ring-shaped electrodes 201 to 210 attached to the outer peripheral surface of the distal end portion 501 of the catheter shaft 50, and a conductive wire 301 connected to each of the ring-shaped electrodes 201 to 210.
- the catheter shaft 50 includes an inner tube 11 having a guide wire lumen 11L, and an outer tube 53 that forms a lumen 12L for inserting the conducting wires 301 to 310 together with the outer peripheral surface of the inner tube 11.
- the outer tube 53 configured and constituting the catheter shaft 50 is a blade tube having a distal end portion 531 reinforced by a resin braid 5315 and a proximal end portion 532 reinforced by a metal braid 5325, and At the tip portion 531 of the tube 53 A side hole 15 extending from the outer peripheral surface to the lumen 12L is formed in the pipe wall corresponding to the mounting position of the ring-shaped electrodes 201 to 210, and the conducting wires 301 to 310 have respective tip portions at the ring-shaped electrodes 201 to 210. In addition to being connected to the ring-shaped electrodes 201 to 210 by being joined to the inner peripheral surface of the tube, it enters the lumen 12L from the side hole 15 and extends to the lumen 12L.
- the catheter shaft 50 constituting the electrode catheter 500 is a double tube structure shaft constituted by the inner tube 11 and the outer tube 53.
- the catheter shaft 50 includes a distal end portion 501 and a proximal end portion 502, and the distal end portion 501 includes a distal end side low hardness region 501A and a hardness inclined region 501B.
- the distal end portion 501 of the catheter shaft 50 has a specific curved shape.
- tip part 501 which actually has a curve shape is illustrated linearly.
- the tip portion 501 having a specific curve shape (stored) is easily deformed by applying an external force (for example, inserting the catheter shaft 50 through the tube), but when the external force is removed, the stored curve is stored. The shape can be restored.
- the effective length (L6) of the catheter shaft 50 is usually 400 to 1500 mm, and is 650 mm if a suitable example is shown.
- the length (L7) of the tip portion 501 is usually 50 to 200 mm, and is 95 mm if a suitable example is shown.
- the length (L8) of the distal-side low hardness region 501A of the distal end portion 501 is usually 20 to 100 mm, and is 45 mm if a suitable example is shown.
- the length (L9) of the hardness gradient region 501B of the tip portion 501 is usually 20 to 100 mm, and is 50 mm if a suitable example is shown.
- the inner tube 11 constituting the catheter shaft 50 is a single lumen tube having a two-layer structure including an inner layer 111 and an outer layer 112, and a guide wire lumen 11 ⁇ / b> L is formed by the inner tube 11.
- the specific configuration of the inner tube 11 is the same as that of the inner tube 11 constituting the catheter shaft 10 of the electrode catheter of the first embodiment.
- the outer tube 53 constituting the catheter shaft 50 is a blade tube having a distal end portion 531 reinforced by a resin braid 5315 and a proximal end portion 532 reinforced by a metal braid 5325. That is, a resin braid 5315 is embedded as a reinforcing material in the distal end portion 531 of the outer tube 53, and a metal braid 5325 is embedded as a reinforcing material in the proximal end portion 532 of the outer tube 53.
- the distal end portion 531 of the outer tube 53 constitutes the distal end portion 501 of the catheter shaft 50, and the proximal end portion 532 of the outer tube 53 constitutes the proximal end portion 502 of the catheter shaft 50.
- the distal end portion 531 of the outer tube 53 is a single lumen tube having a three-layer structure including an inner layer 5311, a reinforcing layer 5313 formed of a braid 5315, and an outer layer 5312.
- the base end portion 532 of the outer tube 53 is a single lumen tube having a three-layer structure including an inner layer 5321, a reinforcing layer 5323 formed by a braid 5325, and an outer layer 5322.
- a lumen 12L is formed by the inner peripheral surface of the outer tube 53 (the distal end portion 531 and the proximal end portion 532) and the outer peripheral surface of the inner tube 11.
- the constituent materials of the inner layers 5311 and 5321 of the outer tube 53 As a constituent material (inner surface resin) of the inner layers 5311 and 5321 of the outer tube 53, synthetic resins such as polyolefin, polyamide, polyether polyamide, polyurethane, nylon, polyether block amide (PEBAX) can be used. Of these, PEBAX is preferably used.
- the constituent materials of the inner layers 5311 and 5321 have the same hardness over the entire length of the catheter shaft 50.
- the hardness of the constituent material of the inner layers 5311 and 5321 is, for example, 72D.
- the thickness of the inner layers 5311 and 5321 is usually 10 to 50 ⁇ m, and 25 ⁇ m is shown as a suitable example.
- the constituent material (outer surface resin) of the outer layers 5312 and 5322 of the outer tube 53 the same kind of resin as the constituent resin of the inner layers 5311 and 5321 can be used, and among these, it is preferable to use PEBAX.
- the constituent materials of the outer layers 5312 and 5322 have different hardness along the length direction of the catheter shaft 50.
- the hardness of the outer layer 5312 (5312a) constituting the distal-side low hardness region 501A of the distal end portion 501 is 35D
- the hardness of the outer layer 5322 constituting the proximal end portion 502 is 72D
- the hardness of the outer layer 5312 (5312b) constituting the hardness gradient region 501B of the distal end portion 501 is changed (decreased) in an inclined manner from 72D to 35D in the distal direction.
- the thickness of the outer layers 5312 and 5322 is usually 30 to 200 ⁇ m, and 95 ⁇ m if a suitable example is shown.
- the reinforcing layer 5313 at the distal end portion 531 of the outer tube 53 includes a resin braid 5315 and a resin 5314 filled in a gap between the resin wires constituting the braid 5315. Further, the reinforcing layer 5323 in the proximal end portion 532 of the outer tube 53 includes a metal braid 5325 and a resin 5324 filled in a gap between metal wires constituting the braid 5325.
- the braid 5315 includes 16 sets (32 pieces) of resin wires arranged at equal angular intervals in the circumferential direction.
- the resin 5314 constituting the reinforcing layer 5313 is a material in which a part of the constituent material of the outer layer 5312 is melted and flows into the gap between the resin wires when the distal end portion 531 of the outer tube 53 is manufactured.
- the constituent material of the braid 5315 (resin wire), the hardness and bending elastic modulus of the constituent material, the wire diameter of the resin wire, the number of strikes and the number of braids 5315 are the same as those of the braid 135 in the electrode catheter 100 of the first embodiment. is there.
- the thickness of the reinforcing layer 5313 is usually 60 to 200 ⁇ m, and 120 ⁇ m if a suitable example is shown.
- the braid 5325 includes 16 sets (32 pieces) of metal wire rods arranged at equiangular intervals in the circumferential direction.
- the resin 5324 constituting the reinforcing layer 5323 is a resin in which a part of the constituent material of the outer layer 5322 is melted and flows into the gap between the resin wires when the base end portion 532 of the outer tube 53 is manufactured.
- the constituent material of the braid 5325 is not particularly limited, and all metal materials used for the blade tube constituting the catheter shaft can be used, and examples include stainless steel wires. it can.
- the wire diameter of the metal wire constituting the braid 5325 is usually 30 to 100 ⁇ m, and 60 ⁇ m is shown as a suitable example. Further, the number of strikes of the braid 5325 is usually 8 to 32, and is 16 if a suitable example is shown. The number of braids 5325 is usually 1 to 4, and 2 is shown as a suitable example. The thickness of the reinforcing layer 5323 is usually 60 to 200 ⁇ m, and is 120 ⁇ m if a suitable example is shown.
- the inner diameter of the outer tube 53 is usually 0.7 to 2.0 mm, and is 1.5 mm as a suitable example.
- the outer diameter of the outer tube 53 is normally 1.3 to 3.0 mm, and is 2.0 mm as a suitable example.
- the distal end portion 531 of the outer tube 53 was obtained by arranging a resin braid 5315 on the outer peripheral surface of the tubular inner layer forming material and arranging the outer layer forming material on the outer peripheral surface of the braid 5315.
- the tubular laminate can be manufactured by heat treatment under a temperature condition equal to or higher than the melting points of the inner layer forming material and the outer layer forming material and lower than the melting point of the resin constituting the braid 5315.
- the proximal end portion 532 of the outer tube 53 is obtained by disposing a metal braid 5325 on the outer peripheral surface of the tubular inner layer forming material and disposing the outer layer forming material on the outer peripheral surface of the braid 5325.
- the tubular laminate can be manufactured by heat treatment under temperature conditions equal to or higher than the melting points of the inner layer forming material and the outer layer forming material.
- the outer tube 53 can be manufactured by joining the distal end portion 531 obtained as described above and the proximal end portion 532 according to a conventional method.
- the ring-shaped electrodes 201 to 210 constituting the electrode catheter 500 are mounted on the outer peripheral surface of the distal end portion 501 (the distal end side low hardness region 501A and the hardness inclined region 501B) of the catheter shaft 50. ing. Lead ends of the conducting wires 301 to 310 are joined to the inner peripheral surfaces of the ring electrodes 201 to 210, respectively.
- a metal having good electrical conductivity such as platinum, gold, silver, aluminum, copper, and stainless steel can be used. From the viewpoint of improving the contrast properties for X-rays, platinum, gold, silver, and alloys containing these as main components are preferable.
- the width of the ring electrodes 201 to 210 (the length in the axial direction of the catheter shaft 50) is, for example, 0.5 to 10 mm. Further, the distance between the electrodes of the ring-shaped electrodes 201 to 210 is, for example, 1 to 10 mm.
- side holes 15 extending from the outer peripheral surface to the lumen 12L are formed in the tube wall of the outer tube 53 at the distal end portion 531 of the catheter shaft 50.
- the conducting wire 301 whose tip is joined to the inner peripheral surface of the ring-shaped electrode 201 enters the lumen 12 ⁇ / b> L from the side hole 15 formed in the tube wall of the outer tube 53.
- 311 is a metal core wire of the conducting wire 301
- 312 is a resin coating layer
- W is a joint.
- a resin wire material (not shown) constituting the braid 5315 is exposed on the inner peripheral surface of the side hole 15. The same applies to the conducting wires 302 to 310 joined to the inner peripheral surfaces of the ring electrodes 202 to 210.
- the distal tip 25 is connected to the distal end side of the catheter shaft 50.
- a through hole is formed in the distal tip 25, and the distal end portion of the inner tube 11 is inserted into the through hole.
- a proximal end portion 502 of the catheter shaft 50 is inserted into the inside (insertion passage) of the handle 40.
- the insertion path of the catheter shaft 50 inside the handle 40 is branched in two directions.
- the conducting wires 301 to 310 extending to the lumen 12L of the catheter shaft 50 are respectively connected to the outer tube 53.
- Each of the proximal ends of the conductors 301 to 310 extends from the proximal end, extends along one branch path, extends from the handle 40, passes through the lumen of the conductor protection tube 51, and is inserted into the connector 41.
- the ring-shaped electrodes 201 to 210 are electrically connected to the terminals in the connector 41, respectively.
- the inner tube 11 constituting the catheter shaft 50 extends from the proximal end of the outer tube 53, extends along the other branch path, extends from the handle 40, and extends from the guide wire protection tube 52. It is connected to the guide wire port 42 through the lumen. Thereby, the guide wire inserted from the guide wire port 42 can be extended from the distal end opening of the distal end tip 25 via the guide wire lumen 11L of the inner tube 11.
- the outer tube 53 constituting the catheter shaft 50 is constituted by the blade tube over the entire length including the distal end portion 531, excellent torque transmission can be exhibited.
- the proximal end portion 532 of the outer tube 53 is reinforced by the metal braid 5325, the torque transmission performance exhibited by the electrode catheter 500 of the present embodiment is the torque transmission of the electrode catheter of the first embodiment. It is even better than the nature.
- the braid 5315 that reinforces the distal end portion 531 of the outer tube 53 is formed from a resin wire, a side hole through which the lead wire of the ring-shaped electrode passes through the tube wall of the outer tube 53 in the distal end portion 531. 15 can be easily formed.
- the resin wire constituting the braid 5315 is unavoidably exposed on the inner peripheral surface of the side hole 15, but unlike the case where the metal wire is exposed, the resin wire makes the side hole 15 The resin coating layer of the inserted lead is not damaged.
- the catheter shaft 50 Since the braid 5315 is embedded in the outer tube 53 in the distal end portion 501, the distal end portion 531 can easily be bent, so that good shaping properties can be exhibited.
- the number of ring-shaped electrodes (the number of conducting wires) is not 10, but may be 2-30, for example.
- a tip electrode may be provided instead of the tip tip 25.
- the number of lumens formed in the distal flexible portion of the catheter shaft is not four, but may be eight or more, for example.
- the number of operation wires may be one (single direction type).
- the braid that reinforces the distal end portion (tip flexible portion) of the catheter shaft may be made of resin (the same braid as the braid 65), and the braid that reinforces the proximal end portion of the catheter shaft may be made of metal.
- the catheter shaft 10 is manufactured using the inner tube 11 obtained by the above (1) and the outer tube 13 obtained by the above (2), and a ring shape is formed on the outer peripheral surface of the distal end portion 101 of the obtained catheter shaft 10.
- the electrodes as shown in FIG. 1 to FIG. 5 are installed through the process of attaching the electrodes 201 to 210 and inserting the conductive wires 301 to 310 connected to the ring electrodes 201 to 210 through the side holes 15 into the lumen 12L.
- An electrode catheter 100 according to the first embodiment of the invention was manufactured.
- the effective length (L1) is 650 mm
- the length (L3) of the distal-side low hardness region 101A of the distal end portion 101 is 50 mm
- the outer layer constituting the distal-side low hardness region 101A The hardness of 132 (132a) is 35D
- the length (L4) of the hardness gradient region 101B is 50 mm
- the hardness of the outer layer 132 (132b) constituting the hardness gradient region 101B changes in an inclined manner from 35D to 72D.
- the hardness of the outer layer 132 (132c) constituting 102 is 72D.
- a comparative electrode catheter was manufactured in the same manner as in Example 1 (3) except that a catheter shaft was produced using the inner tube obtained by (1) and the outer tube obtained by (2). did.
- the effective length is 650 mm
- the hardness of the distal end region (0 to 50 mm from the distal end) is 35D
- the hardness of the rear end region (50 to 100 mm from the distal end) of the distal end portion 101 is Is 55D
- the hardness of the base end portion composed of the stainless blade tube is 72D.
- the electrode catheter obtained in Example 1 is compared with the electrode catheter obtained in Comparative Example 1 (the electrode catheter in which the proximal end portion of the catheter shaft is constituted by a stainless blade tube). It is understood that torque transmission is excellent.
- Electrode catheter 10 Catheter shaft 101 Tip part 101A Tip side low hardness area
- region 102 Base end part 11 Inner tube 111 Inner layer 112 Outer layer 11L Guide wire lumen 12L Lumen 13 Outer tube 131 Inner layer 132 Outer layer 133 Reinforcement layer 134 Resin 135 Braiding 15 Side hole 201 to 210 Ring electrode 25 Tip tip 301 to 310 Conductor 40 Handle 41 Connector 42 Guide wire port 51 Conductor protection tube 52 Guide wire protection tube 200 Electrode catheter 60 Catheter shaft 601 Tip flexible part 61L to 64L Lumen 65 Braiding 67 Inner part 69 Outer part 71 Tip electrode 72 to 74 Ring electrode 81 to 84 Conductor 86 First operation wire 8 7 Second operation wire 90 Control handle 500 Electrode catheter 50 Catheter shaft 501 End portion of catheter shaft 501A Tip side low hardness region 501B Hardness inclined region 502 Base end portion of catheter shaft 53 Outer tube 531 End portion of
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Abstract
Description
複数のリング状電極にそれぞれ接続されている導線は、リング状電極の装着位置に対応してシャフトの管壁に形成されている側孔からカテーテルシャフトのルーメンに進入して当該ルーメンに延在しており、導線の基端は、それぞれ、カテーテルシャフトの基端側に接続されているコネクタの内部に配置された端子に接続されている。
カテーテルシャフトの基端部分をブレードチューブによって構成することにより、電極カテーテルのトルク伝達性をある程度向上させることができる。
本発明の目的は、金属製の編組によって補強されたブレードチューブによりカテーテルシャフトの基端部分が構成されている従来公知の電極カテーテルと比較してトルク伝達性に優れ、カテーテルシャフトの先端部分の管壁にリング状電極の導線を通すための側孔を形成する加工が容易で、形成された側孔に挿通される導線の樹脂被覆層が、側孔の内周面に露出する編組を構成する線材により損傷を受けることのない電極カテーテルを提供することにある。
本発明の他の目的は、ガイドワイヤルーメンを有するカテーテルシャフトを備えたトルク伝達性に優れた電極カテーテルを提供することにある。
前記カテーテルシャフトの先端部分の管壁には前記外周面から前記ルーメンに至る側孔が前記リング状電極の装着位置に対応して形成され、
前記導線は、金属芯線を樹脂被覆してなり、その先端部において前記リング状電極の内周面に接合されることによって当該リング状電極に接続されているとともに、前記側孔から前記ルーメンに進入して当該ルーメンにおいて延在し、
前記カテーテルシャフトは、その全長にわたり編組により補強されたブレードチューブであって、少なくとも前記カテーテルシャフトの先端部分を補強している前記編組が樹脂製であるブレードチューブにより構成されていることを特徴とする。
また、カテーテルシャフトを構成するブレードチューブにおいて、カテーテルシャフトの先端部分を補強している編組が樹脂製であるので、先端部分の管壁にリング状電極の導線を通すための側孔を容易に形成することができる。
また、側孔の内周面に露出する樹脂線材によっては、当該側孔に挿通される導線の樹脂被覆層が損傷を受けることはない。
また、カテーテルシャフトの先端部分にも編組が埋設されていることにより、当該先端部分におけるシェイピング性が向上する。
また、カテーテルシャフトを構成するブレードチューブは、樹脂製の編組によって補強された樹脂チューブであり、すべてが樹脂材料からなるので、先端部分の管壁にリング状電極の導線を通すための側孔を容易に形成することができる。
また、側孔の内周面に露出する樹脂線材によっては、当該側孔に挿通される導線の樹脂被覆層が損傷を受けることはない。
また、カテーテルシャフトの先端部分にも編組が埋設されていることにより、当該先端部分におけるシェイピング性が向上する。
また、カテーテルシャフトの全長にわたり樹脂製の編組により補強されているブレードチューブは、1回の押出成形によって製造することができ、例えば、樹脂製の編組により
補強された先端部分と金属製の編組により補強された基端部分とを接合してなるブレードチューブと比較して製造が容易である。また、編組の構成材料が切り替わるシャフト部分で起こりやすいとされるキンクが起こることもない。
このような構成の電極カテーテルによれば、先端部分を含む全長にわたってカテーテルシャフトがブレードチューブにより構成されているので、優れたトルク伝達性を発揮することができる。
また、カテーテルシャフトを構成するブレードチューブにおいて、先端部分を補強している編組が樹脂製であるので、カテーテルシャフトの先端部分の管壁にリング状電極の導線を通すための側孔を容易に形成することができる。
また、側孔の内周面に露出する樹脂線材によっては、当該側孔に挿通される導線の樹脂被覆層が損傷を受けることはない。
また、カテーテルシャフトの先端部分にも編組が埋設されていることにより、当該先端部分におけるシェイピング性が向上する。
このような構成の電極カテーテルのようにカテーテルシャフトがガイドワイヤルーメンを有し、シャフトを構成する樹脂の割合が低い場合において本発明の構成を採用することは効果的である。
また、カテーテルシャフトの先端部分の管壁にリング状電極の導線を通すための側孔を容易に加工することができ、形成された側孔に挿通される導線の樹脂被覆層が、当該側孔の内周面に露出する樹脂線材によって損傷を受けることはない。
また、本発明の電極カテーテルは、ガイドワイヤルーメンを有するカテーテルシャフトを備えているものであっても、トルク伝達性に優れている。
図1~図5に示すこの実施形態の電極カテーテル100は、心臓の冠動脈などの部位の電位を測定するために用いられるものである。
この電極カテーテル100は、カテーテルシャフト10と、カテーテルシャフト10の先端部分101の外周面に装着されたリング状電極201~210と、リング状電極201~210の各々に接続された導線301~310とを備えてなり、カテーテルシャフト10は、ガイドワイヤルーメン11Lを有する内側チューブ11と、内側チューブ11の外周面とともに導線301~310を挿通するためのルーメン12Lを形成する外側チューブ13とにより構成され、この外側チューブ13は、その全長にわたり樹脂製の編組135によって補強されたブレードチューブからなり、カテーテルシャフト10の先端部分101における外側チューブ13の管壁には、外周面からルーメン12Lに至る側孔15がリング状電極201~210の装着位置に対応して形成され、導線301~310は、それぞれの先端部がリング状電極201~210の内周面に接合されることによって当該リング状電極201~210に接続されているとともに、側孔15からルーメン12Lに進入して当該ルーメン12Lに延在している。
内包するシングルルーメン構造の導線保護チューブ、52は、ガイドワイヤポート42に向けてハンドル40から延び出た内側チューブ11を内包するシングルルーメン構造のガイドワイヤ保護チューブである。
図1に示すように、カテーテルシャフト10の先端部分101は、特定のカーブ形状を有している。なお、図2では、実際はカーブ形状を有する先端部分101を直線的に図示している。
また、先端部分101の長さ(L2)としては、通常50~200mmとされ、好適な一例を示せば95mmとされる。
また、先端部分101の先端側低硬度領域101Aの長さ(L3)としては、通常20~100mmとされ、好適な一例を示せば45mmとされる。
また、先端部分101の硬度傾斜領域101Bの長さ(L4)としては、通常20~100mmとされ、好適な一例を示せば50mmとされる。
内側チューブ11の外径は、通常0.6~1.7mmとされ、好適な一例を示せば1.2mmとされる。
外側チューブ13には、カテーテルシャフト10の全長(先端部分101および基端部分102)にわたり、補強材である樹脂製の編組135が埋設されている。
ここに、内層131の構成材料は、カテーテルシャフト10の全長にわたり同一の硬度を有している。内層131の構成材料の硬度としては、例えば72Dとされる。
内層131の肉厚としては、通常10~50μmとされ、好適な一例を示せば25μmとされる。
外層132の肉厚としては、通常30~200μmとされ、好適な一例を示せば95μmとされる。
補強層133を構成する樹脂134は、外側チューブ13の作製時において、外層132の構成材料の一部が溶融して樹脂線材の隙間に流入されて充填されたものである。
編組135の構成材料の硬度としては、72D以上であることが好ましい。この硬度が過小である場合には、十分な補強効果、延いては良好なトルク伝達性を発揮できない場合がある。
また、編組135の構成材料の曲げ弾性率(ISO178またはJIS K7171)としては、通常500~19,000MPaとされ、好ましくは2,000~7,000MPa、更に好ましくは3,500~4,200とされ、好適な一例を示せば4,200MPaとされる。
また、編組135の打ち数としては、通常8~32とされ、好適な一例を示せば16とされる。
また、編組135の持ち数としては、通常1~4とされ、好適な一例を示せば2とされる。
補強層133の肉厚としては、通常60~200μmとされ、好適な一例を示せば120μmとされる。
外側チューブ13の外径は、通常1.3~3.0mmとされ、好適な一例を示せば2.0mmとされる。
また、リング状電極201~210の電極間距離としては、例えば1~10mmとされる。
リング状電極202~210の内周面に接合されている導線302~310についても同様である。
図5に示すように、先端チップ25には貫通孔26が形成されており、この貫通孔26に内側チューブ11の先端部が挿入されている。
このようにして先端チップ25が接続された内側チューブ11を、外側チューブ13の内部に挿入することにより、二重管構造のカテーテルシャフト10が構成される。
これにより、リング状電極201~210が、それぞれ、コネクタ41内の端子の各々に電気的に接続される。
これにより、ガイドワイヤポート42から挿入するガイドワイヤを、内側チューブ11のガイドワイヤルーメン11Lを経由して、先端チップ25の先端開口から延び出させることができる。
図6は本発明の第2実施形態に係る電極カテーテルを示す側面図であり、図7Aおよび図7Bは、それぞれ、この電極カテーテルを構成するカテーテルシャフトの横断面図である。
シャフト60の先端可撓部分601を第1方向(図1において矢印Aで示す方向)に撓ませるために、その基端を引張操作できる第1操作用ワイヤ86と、カテーテルシャフト60の先端可撓部分601を第2方向(図1において矢印Bで示す方向)に撓ませるために、その基端を引張操作できる第2操作用ワイヤ87と、カテーテルシャフト60の基端側に装着された制御ハンドル90とを備えてなり、カテーテルシャフト60の先端可撓部分601の管壁には外周面からルーメン62Lに至る側孔がリング状電極72~74の装着位置に対応して形成され、導線81~84は金属芯線を樹脂被覆してなり、先端電極71の導線81はルーメン61Lに延在し、リング状電極72~74の導線82~84は、それぞれの先端部がリング状電極72~74の内周面に接合されることによって当該リング状電極72~74に接続されているとともに、側孔からルーメン62Lに進入して、当該ルーメン62Lに延在し、第1操作用ワイヤ86は、その先端部が先端電極71に固定されているとともにルーメン63Lに延在し、第2操作用ワイヤ87は、その先端部が先端電極71に固定されているとともにルーメン64Lに延在してなり、カテーテルシャフト60は、その全長にわたり樹脂製の編組65により補強されたブレードチューブからなる。
また、図7Aおよび図7Bにおいて、67は、カテーテルシャフト60を構成する樹脂からなるインナー(コア)部、69は、インナー67を被覆する樹脂からなるアウター(シェル)部である。
カテーテルシャフト60の長さは、通常400~1500mmとされ、好ましくは700~1200mmとされる。
先端可撓部分601の長さは、例えば30~300mmとされ、好ましくは50~250mmとされる。
また、制御ハンドル90には、カテーテルシャフト60の先端可撓部分601を曲げる操作を行うための摘み95が装着してある。
マルチルーメン構造のブレードチューブである。
インナー部67を構成する樹脂の硬度としては、例えば25D~40Dとされる。
ルーメン61Lには、先端電極71に接続された導線81が挿通されており、ルーメン62Lには、リング状電極72~74の各々に接続された導線82~84が挿通されている。
アウター部69を構成する樹脂材料としては、熱可塑性ポリアミド系エラストマーを挙げることができ、特に、ポリエーテルブロックアミド(PEBAX)が好ましい。
図7Aおよび図7Bに示す断面視において、編組65は、16組(32本)の樹脂線材が円周方向に等角度間隔で配置されてなる。
作可能になっている。
一方、制御ハンドル90の摘み95を図6に示すB1方向に回転させると、第2操作用ワイヤ87が引っ張られてルーメン64Lの基端側に移動し、先端可撓部分601を第2方向(矢印Bで示す方向)に撓ませることができる。
図9~図12に示すこの実施形態の電極カテーテル500は、心臓の冠動脈などの部位の電位を測定するために用いられるものである。
なお、図9~図12において、図1~図4と同一の符号で示した部分は、第1実施形態の電極カテーテルと同様の構成である。
図9に示すように、カテーテルシャフト50の先端部分501は、特定のカーブ形状を有している。なお、図10では、実際はカーブ形状を有する先端部分501を直線的に図示している。
また、先端部分501の長さ(L7)としては、通常50~200mmとされ、好適な一例を示せば95mmとされる。
また、先端部分501の先端側低硬度領域501Aの長さ(L8)としては、通常20~100mmとされ、好適な一例を示せば45mmとされる。
また、先端部分501の硬度傾斜領域501Bの長さ(L9)としては、通常20~100mmとされ、好適な一例を示せば50mmとされる。
内側チューブ11の具体的な構成は、第1実施形態の電極カテーテルのカテーテルシャフト10を構成する内側チューブ11と同様である。
すなわち、外側チューブ53の先端部分531には、樹脂製の編組5315が補強材として埋設され、外側チューブ53の基端部分532には、金属製の編組5325が補強材として埋設されている。
そして、外側チューブ53の先端部分531は、カテーテルシャフト50の先端部分501を構成し、外側チューブ53の基端部分532は、カテーテルシャフト50の基端部分502を構成する。
また、図11Cに示すように、外側チューブ53の基端部分532は、内層5321と、編組5325による補強層5323と、外層5322とからなる三層構成のシングルルーメンチューブである。
この外側チューブ53(先端部分531および基端部分532)の内周面と内側チューブ11の外周面とによりルーメン12Lが形成されている。
ここに、内層5311,5321の構成材料は、カテーテルシャフト50の全長にわたり同一の硬度を有している。内層5311,5321の構成材料の硬度としては、例えば72Dとされる。
内層5311,5321の肉厚としては、通常10~50μmとされ、好適な一例を示せば25μmとされる。
外層5312,5322の肉厚としては、通常30~200μmとされ、好適な一例を示せば95μmとされる。
また、外側チューブ53の基端部分532における補強層5323は、金属製の編組5325と、この編組5325を構成する金属線材の隙間に充填された樹脂5324とからなる。
補強層5313を構成する樹脂5314は、外側チューブ53の先端部分531の作製時において、外層5312の構成材料の一部が溶融して樹脂線材の隙間に流入されて充填されたものである。
補強層5323を構成する樹脂5324は、外側チューブ53の基端部分532の作製時において、外層5322の構成材料の一部が溶融して樹脂線材の隙間に流入されて充填されたものである。
でき、ステンレス素線などを例示することができる。
また、編組5325の打ち数としては、通常8~32とされ、好適な一例を示せば16とされる。
また、編組5325の持ち数としては、通常1~4とされ、好適な一例を示せば2とされる。
補強層5323の肉厚としては、通常60~200μmとされ、好適な一例を示せば120μmとされる。
外側チューブ53の外径は、通常1.3~3.0mmとされ、好適な一例を示せば2.0mmとされる。
また、リング状電極201~210の電極間距離としては、例えば1~10mmとされる。
301は、外側チューブ53の管壁に形成された側孔15からルーメン12Lに進入し、このルーメン12Lを延在する。同図において、311は、導線301の金属芯線、312は樹脂被覆層、Wは接合部である。なお、側孔15の内周面には、編組5315を構成する樹脂線材(図示せず)が露出している。
リング状電極202~210の内周面に接合されている導線302~310についても同様である。
先端チップ25には貫通孔が形成されており、この貫通孔に内側チューブ11の先端部が挿入されている。
このようにして先端チップ25が接続された内側チューブ11を、外側チューブ53の内部に挿入することにより、二重管構造のカテーテルシャフト50が構成される。
これにより、リング状電極201~210が、それぞれ、コネクタ41内の端子の各々に電気的に接続される。
これにより、ガイドワイヤポート42から挿入するガイドワイヤを、内側チューブ11のガイドワイヤルーメン11Lを経由して、先端チップ25の先端開口から延び出させることができる。
また、外側チューブ53の基端部分532が金属製の編組5325によって補強されていることにより、本実施形態の電極カテーテル500により発揮されるトルク伝達性は、第1実施形態の電極カテーテルのトルク伝達性よりも更に優れている。
チューブ53に編組5315が埋設されていることによって当該先端部分531に折り曲げ癖が付きやすくなっているので、良好なシェイピング性を発揮することができる。
例えば、第1実施形態および第3実施形態の電極カテーテルにおいて、リング状電極の個数(導線の本数)は10ではなく、例えば2~30であってもよい。
また、先端チップ25に代えて先端電極を備えていてもよい。
また、操作用ワイヤの数は1本(シングルディレクションタイプ)であってもよい。
また、カテーテルシャフトの先端部分(先端可撓部分)を補強する編組を樹脂製(編組65と同様の編組)とし、カテーテルシャフトの基端部分を補強する編組を金属製としてもよい。
(1)内側チューブの作製:
高密度ポリエチレンからなる厚さ30μmの内層111と、PEBAX(硬度55D)からなる厚さ60μmの外層112とによる二層構成の内側チューブ11(内径=1.0mm,外径=1.18mm)を作製した。
PEBAX(硬度72D)からなる管状の内層形成材料の外周面上に、線径60μmのPEEK樹脂線材からなる編組135(打ち数=16,持ち数=2)を配置し、この編組135の外周面上にPEBAXからなる外層形成材料を配置し、このようにして得られた管状積層体を加熱処理することにより、厚さ25μmの内層131と、厚さ120μmの補強層133と、厚さ95μmの外層132とによる三層構成の外側チューブ13(内径=1.5mm,外径=2.0mm)を作製した。
上記(1)により得られた内側チューブ11および上記(2)により得られた外側チューブ13を使用してカテーテルシャフト10を作製し、得られたカテーテルシャフト10の先端部分101の外周面にリング状電極201~210を装着するとともに、リング状電極201~210の各々に接続された導線301~310を側孔15を通してルーメン12Lに挿通させる工程を経て、図1~図5に示したような本発明の第1実施形態に係る電極カテーテル100を製造した。
(1)実施例1(1)と同様にして内側チューブを作製した。
PEBAX(硬度72D)からなる管状の内層形成材料の、先端から100mmの部分を除いた外周面上に、線径50μmのステンレス線材からなる編組(打ち数=16,持ち
数=1)を配置し、更に、内層形成材料の全長にわたり、PEBAXからなる外層形成材料を配置し、得られた管状積層体を加熱処理することにより、ステンレスブレードチューブから基端部分が構成され、編組で補強されていない樹脂チューブから先端部分が構成されてなる外側チューブ(内径=1.5mm,外径=2.0mm)を作製した。
上記(1)により得られた内側チューブおよび上記(2)により得られた外側チューブを使用してカテーテルシャフトを作製したこと以外は実施例1(3)と同様にして比較用の電極カテーテルを製造した。
実施例1および比較例1によって得られた電極カテーテルの各々について、カテーテルシャフトの先端を固定した状態でハンドルを軸回りに回転させ、この回転に伴って先端に伝達されたトルクをトルクゲージにより測定した。結果(ハンドルの回転角度とトルクとの関係)を図8に示す。
10 カテーテルシャフト
101 先端部分
101A 先端側低硬度領域
101B 硬度傾斜領域
102 基端部分
11 内側チューブ
111 内層
112 外層
11L ガイドワイヤルーメン
12L ルーメン
13 外側チューブ
131 内層
132 外層
133 補強層
134 樹脂
135 編組
15 側孔
201~210 リング状電極
25 先端チップ
301~310 導線
40 ハンドル
41 コネクタ
42 ガイドワイヤポート
51 導線保護チューブ
52 ガイドワイヤ保護チューブ
200 電極カテーテル
60 カテーテルシャフト
601 先端可撓部分
61L~64L ルーメン
65 編組
67 インナー部
69 アウター部
71 先端電極
72~74 リング状電極
81~84 導線
86 第1操作用ワイヤ
87 第2操作用ワイヤ
90 制御ハンドル
500 電極カテーテル
50 カテーテルシャフト
501 カテーテルシャフトの先端部分
501A 先端側低硬度領域
501B 硬度傾斜領域
502 カテーテルシャフトの基端部分
53 外側チューブ
531 外側チューブの先端部分
5311 内層
5312 外層
5313 補強層
5314 樹脂
5315 樹脂製の編組
532 外側チューブの基端部分
5321 内層
5322 外層
5323 補強層
5324 樹脂
5325 金属製の編組
Claims (6)
- 少なくとも1つのルーメンを有するカテーテルシャフトと、前記カテーテルシャフトの先端部分の外周面に装着された少なくとも1つのリング状電極と、前記リング状電極に接続された導線とを備えてなり、
前記カテーテルシャフトの先端部分の管壁には前記外周面から前記ルーメンに至る側孔が前記リング状電極の装着位置に対応して形成され、
前記導線は、金属芯線を樹脂被覆してなり、その先端部において前記リング状電極の内周面に接合されることによって当該リング状電極に接続されているとともに、前記側孔から前記ルーメンに進入して当該ルーメンにおいて延在し、
前記カテーテルシャフトは、その全長にわたり編組により補強されたブレードチューブであって、少なくとも前記カテーテルシャフトの先端部分を補強している前記編組が樹脂製であるブレードチューブにより構成されていることを特徴とする電極カテーテル。 - 前記カテーテルシャフトは、その全長にわたり樹脂製の編組により補強された前記ブレードチューブにより構成されていることを特徴とする請求項1に記載の電極カテーテル。
- 前記カテーテルシャフトは、樹脂製の編組により補強された先端部分と、金属製の編組により補強された基端部分とを有する前記ブレードチューブにより構成されていることを特徴とする請求項1に記載の電極カテーテル。
- 前記カテーテルシャフトがガイドワイヤルーメンを有することを特徴とする請求項1~3の何れかに記載の電極カテーテル。
- 前記カテーテルシャフトは、ガイドワイヤルーメンを有する内側チューブと、前記内側チューブの外周面とともに前記導線を挿通するためのルーメンを形成する外側チューブとを備えてなり、前記外側チューブが前記ブレードチューブであることを特徴とする請求項1~3の何れかに記載の電極カテーテル。
- 前記カテーテルシャフトは、前記編組の内側に複数のルーメンを有するマルチルーメンチューブであることを特徴とする請求項1~3の何れかに記載の電極カテーテル。
Priority Applications (4)
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CN201680082506.9A CN108697355A (zh) | 2016-02-25 | 2016-12-16 | 电极导管 |
CA3013421A CA3013421A1 (en) | 2016-02-25 | 2016-12-16 | Electrode catheter |
EP16891658.3A EP3420897B1 (en) | 2016-02-25 | 2016-12-16 | Electrode catheter |
US16/109,572 US20180360333A1 (en) | 2016-02-25 | 2018-08-22 | Electrode catheter |
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JP2016034868 | 2016-02-25 | ||
JP2016-034868 | 2016-02-25 | ||
JP2016-104152 | 2016-05-25 | ||
JP2016104152A JP6541268B2 (ja) | 2016-02-25 | 2016-05-25 | 電極カテーテル |
Related Child Applications (1)
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US16/109,572 Continuation US20180360333A1 (en) | 2016-02-25 | 2018-08-22 | Electrode catheter |
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WO2017145503A1 true WO2017145503A1 (ja) | 2017-08-31 |
Family
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PCT/JP2016/087523 WO2017145503A1 (ja) | 2016-02-25 | 2016-12-16 | 電極カテーテル |
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US (1) | US20180360333A1 (ja) |
EP (1) | EP3420897B1 (ja) |
JP (1) | JP6541268B2 (ja) |
CN (1) | CN108697355A (ja) |
CA (1) | CA3013421A1 (ja) |
TW (1) | TWI624247B (ja) |
WO (1) | WO2017145503A1 (ja) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
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US20210378573A1 (en) * | 2019-03-25 | 2021-12-09 | Japan Lifeline Co., Ltd. | Catheter |
Families Citing this family (5)
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US11571569B2 (en) | 2019-02-15 | 2023-02-07 | Pulse Biosciences, Inc. | High-voltage catheters for sub-microsecond pulsing |
WO2020261716A1 (ja) * | 2019-06-25 | 2020-12-30 | 株式会社カネカ | カテーテルおよびその製造方法 |
CN111150933B (zh) * | 2019-09-02 | 2022-08-09 | 杭州神络医疗科技有限公司 | 导管电极和体内植入神经刺激装置 |
WO2022190300A1 (ja) * | 2021-03-10 | 2022-09-15 | 日本ライフライン株式会社 | 電極カテーテル |
JP2024049769A (ja) | 2022-09-29 | 2024-04-10 | 日本ライフライン株式会社 | 電極カテーテル及びカテーテルシャフトの製造方法 |
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2016
- 2016-05-25 JP JP2016104152A patent/JP6541268B2/ja active Active
- 2016-12-16 EP EP16891658.3A patent/EP3420897B1/en active Active
- 2016-12-16 CA CA3013421A patent/CA3013421A1/en not_active Abandoned
- 2016-12-16 CN CN201680082506.9A patent/CN108697355A/zh active Pending
- 2016-12-16 WO PCT/JP2016/087523 patent/WO2017145503A1/ja active Application Filing
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2017
- 2017-01-10 TW TW106100723A patent/TWI624247B/zh not_active IP Right Cessation
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2018
- 2018-08-22 US US16/109,572 patent/US20180360333A1/en not_active Abandoned
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Also Published As
Publication number | Publication date |
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US20180360333A1 (en) | 2018-12-20 |
TWI624247B (zh) | 2018-05-21 |
EP3420897A1 (en) | 2019-01-02 |
CN108697355A (zh) | 2018-10-23 |
JP2017148472A (ja) | 2017-08-31 |
CA3013421A1 (en) | 2017-08-31 |
EP3420897A4 (en) | 2019-03-13 |
EP3420897B1 (en) | 2022-03-16 |
JP6541268B2 (ja) | 2019-07-10 |
TW201735862A (zh) | 2017-10-16 |
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