WO2020194474A1 - カテーテル - Google Patents
カテーテル Download PDFInfo
- Publication number
- WO2020194474A1 WO2020194474A1 PCT/JP2019/012621 JP2019012621W WO2020194474A1 WO 2020194474 A1 WO2020194474 A1 WO 2020194474A1 JP 2019012621 W JP2019012621 W JP 2019012621W WO 2020194474 A1 WO2020194474 A1 WO 2020194474A1
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- WIPO (PCT)
- Prior art keywords
- catheter
- side hole
- catheter shaft
- braid
- ring
- Prior art date
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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
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
- A61M25/0053—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids having a variable stiffness along the longitudinal axis, e.g. by varying the pitch of the coil or braid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
-
- 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
- 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
- A61B5/24—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
- A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
-
- 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
- A61B5/296—Bioelectric electrodes therefor specially adapted for particular uses for electromyography [EMG]
-
- 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
- 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
-
- 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
-
- 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
- A61M25/0052—Localized reinforcement, e.g. where only a specific part of the catheter is reinforced, for rapid exchange guidewire port
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B2018/1467—Probes or electrodes therefor using more than two electrodes on a single probe
-
- 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
- A61M2025/0059—Catheters; Hollow probes characterised by structural features having means for preventing the catheter, sheath or lumens from collapsing due to outer forces, e.g. compressing forces, or caused by twisting or kinking
-
- 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
- A61M2230/00—Measuring parameters of the user
- A61M2230/04—Heartbeat characteristics, e.g. ECG, blood pressure modulation
-
- 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
- A61M25/0045—Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
Definitions
- the present invention relates to a catheter comprising a catheter shaft reinforced by a braid woven with a metal wire or a metal wire bundle.
- an electrode catheter in which the base end portion of a catheter shaft is formed by a resin tube (blade tube) reinforced by a metal braid such as stainless steel is known (see, for example, Patent Document 1 below).
- a resin tube blade tube
- a metal braid such as stainless steel
- an electrode catheter having a catheter shaft composed of a blade tube reinforced by a resin braid over its entire length (claim 2 of Patent Document 2), a tip portion reinforced by a resin braid, and a metal.
- an electrode catheter (claim 3 of Patent Document 2) provided with a catheter shaft having a proximal end portion reinforced by a braided material.
- a catheter equipped with a catheter shaft reinforced with a resin braid over its entire length cannot sufficiently improve torque transmission because the braid that reinforces the proximal end portion is also made of resin.
- a catheter having a catheter shaft having a tip portion reinforced by a resin braid and a proximal end portion reinforced by a metal braid has a resin blade tube constituting the distal end portion and a proximal end portion. Since it is manufactured by fusing the metal blade tubes that compose it, the resin braid that reinforces the tip part and the metal braid that reinforces the base end part are not continuous, so torque transmission is possible. It cannot be improved sufficiently. Further, in a catheter having such a configuration, kinking is likely to occur at the boundary between the distal end portion and the proximal end portion where the constituent materials of the braid are switched.
- the cut surface of the metal wire forming the braid is exposed on the inner peripheral surface of the side hole, and the metal wire is exposed during the manufacture and use of the catheter.
- the cut surface extends into the side hole and comes into contact with the lead wire of the ring-shaped electrode, the resin coating layer constituting the lead wire is damaged, the insulation property of the lead wire is impaired, or the lead wire is broken. It is possible that it will happen.
- An object of the present invention is that it has excellent torque transmission as compared with a conventionally known catheter, and it is easy to process a side hole for passing a lead wire of a ring-shaped electrode in a tube wall at the tip of a catheter shaft. It is an object of the present invention to provide a catheter in which the resin coating layer of the lead wire to be inserted into the hole is not peeled off or the lead wire is not broken.
- the catheter of the present invention comprises a catheter shaft having at least one lumen, at least one ring-shaped electrode mounted on the outer peripheral surface of the tip portion of the catheter shaft, and a metal core wire coated with resin, and the ring-shaped electrode.
- a catheter with a lead wire connected to The catheter shaft is a blade tube in which a braid formed of a metal wire or a metal wire bundle is embedded in a tube wall over the entire length.
- a side hole extending from the outer peripheral surface to the lumen corresponds to the mounting position of the ring-shaped electrode to cut the metal wire or the metal wire bundle.
- the lead wire is connected to the ring-shaped electrode by joining the tip end portion to the inner peripheral surface of the ring-shaped electrode, and passes through the mesh of the braid by being inserted into the side hole. , Entering the lumen of the catheter shaft and extending in the lumen, The side hole through which the lead wire is inserted is filled with a resin material.
- the diameter of the lead wire is d and the length of the diagonal line of the mesh of the braid in the axial direction is G
- the value of G / d is 1.2 or more.
- the entire length of the catheter shaft is reinforced with a braid formed of metal strands (bundles), so that the catheter is excellent in torque transmission as compared with a conventionally known catheter.
- the side hole penetrating the tube wall of the catheter shaft can be formed without cutting the metal wire (bundle), the side hole can be easily formed.
- the diagonal length (G) of the braided mesh is 1.2 times or more the diameter (d) of the lead wire, even if the metal strands (bundles) are present in the side holes, the said The lead wire can be passed through the braided mesh while avoiding contact with the metal wire (bundle).
- the G / d value is preferably 1.2 to 33.
- the G / d value is 1.2 to 33, it is possible to prevent the resin coating layer of the lead wire from peeling off or the lead wire from being broken, and to sufficiently secure the reinforcing effect by braiding. can do.
- the opening diameter of the side hole or the opening length of the side hole in the axial direction of the catheter shaft is P, and the electrode of the ring-shaped electrode mounted at the formation position of the side hole.
- W it is preferable that the following equations (1) and (2) are satisfied.
- the "opening diameter of the side hole” means the diameter of the opening of the side hole when the side hole is a round hole
- the "opening length of the side hole” means that the side hole is a long hole (length). The length of the opening in the shaft axial direction of the side hole when it is a hole).
- Equation (1) 1.0d ⁇ P ⁇ 0.9W Equation (2): 0.1 ⁇ P / G ⁇ 4.0
- the catheter having such a configuration when the opening diameter (opening length) P of the side hole is 1.0 d or more, it is possible to secure the insertion of the lead wire into the side hole. Further, when the opening diameter (opening length) P of the side hole is 0.9 W or less, the opening of the side hole on the outer peripheral surface of the shaft can be reliably closed by the ring-shaped electrode.
- the P / G value is 0.1 or more, even if the metal wire (bundle) is present in the side hole, the lead wire is prevented from coming into contact with the metal wire (bundle). Can be passed through the side hole. Further, when the P / G value is 4.0 or less, the operation of filling the side holes with the resin material at the time of manufacturing can be easily performed.
- the diameter of the metal wire (wire with a circular cross section), the width of the metal wire (wire with a rectangular cross section), or the width of the bundle of metal wires is 0.03 to 0. It is preferably 1 mm and the density of the braid at least at the tip of the catheter shaft is 13-265 PPI.
- a braid is formed of metal strands (bundles) having a diameter or width of 0.03 to 0.1 mm, and the density of the braid at the tip of the catheter shaft is 13 PPI or more.
- the braid can exert a sufficient reinforcing effect and, by extension, an effect of improving torque transmission.
- a braid is formed by metal strands (bundles) having a diameter or width of 0.03 to 0.1 mm, and the density of the braid at the tip of the catheter shaft is 265 PPI or less, so that the diagonal of the braided mesh is
- the length (G) can be made sufficiently long, and the G / d value can be surely set to 1.2 or more (lead wires can be passed through the braided mesh).
- the catheter of the present invention has excellent torque transmission as compared with a conventionally known catheter, and at the time of manufacture, a side hole for passing a lead wire of a ring-shaped electrode is easily formed in a tube wall at the tip of a catheter shaft. Therefore, the resin coating layer of the lead wire does not peel off or the lead wire does not break during manufacturing and use.
- FIG. 1 It is a side view which shows the electrode catheter which concerns on 1st Embodiment of this invention. It is a side view which shows the catheter shaft which comprises the electrode catheter shown in FIG. It is sectional drawing (IIIA-IIIA sectional view) of the catheter shaft shown in FIG. It is a cross-sectional view (IIIB-IIIB cross-sectional view) of the catheter shaft shown in FIG. It is a cross-sectional view (IIIC-IIIC cross-sectional view) of the catheter shaft shown in FIG. It is sectional drawing which shows typically the form in which the lead wire of a ring-shaped electrode has entered the lumen of a catheter shaft through a side hole in the electrode catheter shown in FIG. It is sectional drawing which shows the connection state of the inner tube which constitutes the catheter shaft shown in FIG. 2 and the tip
- the electrode catheter 100 of this embodiment shown in FIGS. 1 to 6 is used for measuring the electric potential of a site such as a coronary artery of the heart.
- the electrode catheter 100 includes lead wires 301 to 310 connected to the catheter shaft 10, ring-shaped electrodes 201 to 210 attached to the outer peripheral surface of the tip portion 101 of the catheter shaft 10, and ring-shaped electrodes 201 to 210, respectively.
- the catheter shaft 10 is composed of an inner tube 11 having a guide wire lumen 11L and an outer tube 13 forming a lumen 12L for inserting lead wires 301 to 310 together with the outer peripheral surface of the inner tube 11.
- a braid 183 formed of a metal wire bundle 181 is embedded in the tube wall of the outer tube 13 over the entire length of the catheter shaft 10, and is formed in the tube wall of the outer tube 13 at the tip portion 101 of the catheter shaft 10.
- Side holes 15 extending from the outer peripheral surface to the lumen 12L are formed corresponding to the mounting positions of the ring-shaped electrodes 201 to 210 without cutting the metal wire bundle 181, and the lead wires 301 to 310 are the respective tip portions. Is electrically connected to the ring-shaped electrodes 201 to 210 by being joined to the inner peripheral surfaces of the ring-shaped electrodes 201 to 210, and side holes corresponding to the mounting positions of the ring-shaped electrodes 201 to 210.
- the side through which each of the lead wires 301 to 310 is inserted passes through the mesh of the braid 183 by being inserted into the 15 and enters the lumen 12L through the side hole 15 and extends to the lumen 12L.
- the holes 15 are filled with a resin material (adhesive) 16, and the diameters of the lead wires 301 to 310 are d, and the diagonal length of the mesh of the braid 183 in the axial direction of the catheter shaft 10 is G. When this is done, the value of G / d is 1.2 to 33.
- 25 is a tip 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 the proximal end portion of each of the lead wires 301 to 310.
- 42 is a guide wire port
- 51 is a lead wire protection tube having a single lumen structure containing lead wires 301 to 310 extending from the handle 40 toward the connector 41, a connector having a plurality of terminals to which the connector is connected.
- Reference numeral 52 denotes a guide wire protection tube having a single lumen structure, which includes an 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 shaft having a double tube structure composed of an inner tube 11 and an outer tube 13.
- the catheter shaft 10 is composed of a tip end portion 101 and a base end portion 102, and the tip end portion 101 is composed of a tip side low hardness region 101A and a hardness inclination region 101B.
- the tip portion 101 of the catheter shaft 10 has a specific curved shape.
- the tip portion 101 which actually has a curved shape is shown linearly.
- the tip portion 101 having (remembering) a specific curve shape is easily deformed by applying an external force (for example, inserting the catheter shaft 10 into the tube), but when the external force is removed, the stored curve It can be restored to its shape.
- an external force for example, inserting the catheter shaft 10 into the tube
- the effective length (L1) of the catheter shaft 10 is usually 400 to 1500 mm, and a suitable example is 650 mm.
- the length (L2) of the tip portion 101 is usually 50 to 200 mm, and a suitable example is 95 mm.
- the length (L3) of the low hardness region 101A on the tip side of the tip portion 101 is usually 20 to 100 mm, and a suitable example is 45 mm.
- the length (L4) of the hardness inclination region 101B of the tip portion 101 is usually 20 to 100 mm, and a suitable example is 50 mm.
- the inner tube 11 constituting the catheter shaft 10 is a two-layer single lumen tube composed of an inner layer 111 and an outer layer 112, and the guide wire lumen 11L is formed by the inner tube 11.
- high-density polyethylene or the like can be used as the constituent material of the inner layer 111.
- polyether block amide (PEBAX) or the like can be used as a constituent material of the outer layer 112 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 a suitable example is 1.0 mm.
- the outer diameter of the inner tube 11 is usually 0.6 to 1.7 mm, and a suitable example is 1.2 mm.
- a braid 183 formed of a metal wire bundle 181 is embedded as a reinforcing material in the tube wall of the outer tube 13 constituting the catheter shaft 10 over the entire length of the catheter shaft 10 (tip portion 101 and proximal end portion 102). .. That is, the outer tube 13 is made of a blade tube which is a resin tube reinforced by a metal braid 183.
- the outer tube 13 is a three-layer single lumen tube composed of an inner layer 131, a reinforcing layer 133 made of a braid 183, and an outer layer 132, and the inner peripheral surface of the outer tube 13 is formed.
- a lumen 12L is formed by the outer peripheral surface of the inner tube 11.
- the constituent material (inner surface resin) of the inner layer 131 of the outer tube 13 synthetic resins such as polyolefin, polyamide, polyether polyamide, polyurethane, nylon, and polyether block amide (PEBAX) can be used, and among these, synthetic resins can be used. It is preferable 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 a suitable example is 25 ⁇ m.
- constituent material (outer surface resin) of the outer layer 132 of the outer tube 13 a resin of the same type as the constituent resin of the inner layer 131 can be used, and among these, PEBAX is preferably used.
- the constituent materials of the outer layer 132 have different hardnesses along the length direction of the catheter shaft 10.
- the hardness of the outer layer 132 (132a) forming the tip-side low hardness region 101A of the tip portion 101 is 35D
- the hardness of the outer layer 132 (132c) forming the base end portion 102 is 72D
- the hardness of the outer layer 132 (132b) constituting the hardness inclination region 101B of the tip portion 101 is inclined (decreased) from 72D to 35D toward the tip direction.
- the wall thickness of the outer layer 132 is usually 30 to 200 ⁇ m, and a suitable example is 95 ⁇ m.
- the reinforcing layer 133 of the outer tube 13 is composed of a metal braid 183 and a resin 134 filled in the gap between the metal wire bundles 181 constituting the braid 183.
- the braid 183 has 16 strokes and 2 holdings, and in the cross-sectional view shown in FIGS. 3A to 3C, the metal wire bundles 181 each consisting of two metal wires are equiangular in the circumferential direction. 16 pieces are arranged at (22.5 °) intervals.
- the number of braids to reinforce the outer tube 13 and the number of holdings can be changed as appropriate.
- the number of strokes is preferably 8 to 32, and the number of braids is preferably 1 to 4.
- the resin 134 constituting the reinforcing layer 133 is filled by melting a part of the constituent materials of the outer layer 132 and flowing into the gaps of the resin wire rod at the time of manufacturing the outer tube 13.
- the constituent material of the braid 183 is not particularly limited, and all known metal materials constituting the blade tube can be used, and examples thereof include stainless steel.
- the wall thickness of the reinforcing layer 133 is usually 60 to 200 ⁇ m, and a suitable example is 120 ⁇ m.
- the width (W181 shown in FIG. 6) of the metal wire bundle 181 constituting the braid 183 is preferably 0.04 to 0.2 mm, and a suitable example is 0.12 mm.
- the wire diameter (W181 / number of holdings) of the metal wire constituting the metal wire bundle 181 is usually 0.02 to 0.1 mm, and a suitable example is 0.06 mm (0.12 mm / 2). ).
- the inner diameter of the outer tube 13 is usually 0.7 to 2.0 mm, and a suitable example is 1.5 mm.
- the outer diameter of the outer tube 13 is usually 1.3 to 3.0 mm, and a suitable example is 2.0 mm.
- the outer tube 13 which is a blade tube forms a braid 183 on the outer peripheral surface of the tubular inner layer forming material, arranges the outer layer forming material on the outer peripheral surface of the braid 183, and the tubular laminate thus obtained. Can be produced by heating above the melting points of the inner layer forming material and the outer layer forming material.
- the ring-shaped electrodes 201 to 210 constituting the electrode catheter 100 are mounted on the outer peripheral surfaces of the tip portion 101 (tip side low hardness region 101A and hardness inclination region 101B) of the catheter shaft 10. ing.
- the tip portions of the lead wires 301 to 310 are joined to the inner peripheral surfaces of the ring-shaped 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 property with respect to X-rays, platinum, gold, silver and alloys containing these as main components are preferable.
- the width of the ring-shaped electrodes 201 to 210 (W shown in FIG. 6; the length of the catheter shaft 10 in the axial direction) is preferably 0.5 to 10 mm, and a suitable example is 1 mm.
- the distance between the ring-shaped electrodes 201 to 210 is, for example, 1 to 10 mm.
- ten side holes extending from the outer peripheral surface of the outer tube 13 to the lumen 12L are made of metal, corresponding to the mounting positions of the ring-shaped electrodes 201 to 210.
- the wire bundle 181 (metal wire bundle 181 passing through the position where the side hole 15 should be formed) is formed without being cut.
- the lead wire 301 whose tip end is joined to the inner peripheral surface of the ring-shaped electrode 201 is inserted into the side hole 15 formed corresponding to the mounting position of the ring-shaped electrode 201. As a result, it passes through the mesh of the braid (not shown in FIG. 4), enters the lumen 12L from the side hole 15, and extends the lumen 12L.
- 311 is a metal core wire of the lead wire 301
- 312 is a resin coating layer
- 16 is a resin material (adhesive) filled in the side hole 15 through which the lead wire 301 is inserted.
- the braid (metal wire bundle) embedded in the tube wall of the outer tube 13 is omitted in FIG. 4, the lead wire 301 and the metal wire bundle are not in contact with each other.
- the lead wires 302 to 310 joined to the inner peripheral surfaces of the ring-shaped electrodes 202 to 210 are the same as those shown in FIG.
- the diameter (d) of the lead wires 301 to 310 is preferably 0.04 to 0.15 mm, and a suitable example is 0.1 mm.
- a tip tip 25 is connected to the tip end side of the catheter shaft 10. As shown in FIG. 5, a through hole 26 is formed in the tip tip 25, and the tip portion of the inner tube 11 is inserted into the through hole 26. By inserting the inner tube 11 to which the tip tip 25 is connected into the inside of the outer tube 13 in this way, the catheter shaft 10 having a double tube structure is configured.
- the proximal end portion of the catheter shaft 10 is inserted inside the handle 40 (insertion passage).
- the insertion passage of the catheter shaft 10 inside the handle 40 is branched in two directions, and the lead wires 301 to 310 extending to the lumen 12L of the catheter shaft 10 inside the handle 40 are the outer tubes 13, respectively. Extends from the proximal end of the lead wire, extends along one branch path, extends from the handle 40, passes through the lumen of the lead wire protection tube 51, is inserted into the connector 41, and is the proximal end of the lead wires 301 to 310.
- Each of the portions is connected to each of a plurality of terminals built in the connector 41.
- the ring-shaped electrodes 201 to 210 are electrically connected to each of the terminals in the connector 41, respectively.
- the inner tube 11 constituting the catheter shaft 10 extends from the base end of the outer tube 13 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. As a result, the guide wire inserted from the guide wire port 42 can be extended from the tip opening of the tip tip 25 via the guide wire lumen 11L of the inner tube 11.
- FIG. 6 shows the diameter (d) of the lead wire 301, the diagonal length (G) of the mesh of the braid 183 in the axial direction of the catheter shaft 10, and the opening length (P) of the side hole 15 in the same direction. It is a schematic diagram for demonstrating the relationship between the width (W) of the ring-shaped electrode 201, and the width (W181) of the metal wire bundle 181 constituting the braid 183.
- the lead wires 302 to 310 joined to the inner peripheral surfaces of the ring-shaped electrodes 202 to 210 are also the same as those shown in FIG.
- the metal wire bundle 181 is woven to form a braid 183 having a rhombic mesh.
- the diagonal length (G) of the mesh of the braid 183 is preferably 0.07 to 1.3 mm, and a suitable example is 0.3 mm.
- a long hole (long hole) -shaped side hole 15 is formed corresponding to the mounting position of the ring-shaped electrode 201 without cutting the metal wire bundle 181.
- a metal wire bundle 181 exists in the side hole 15.
- the opening length (P) of the side hole 15 in the axial direction of the catheter shaft 10 is preferably 0.04 to 9.9 mm, and a suitable example is 0.5 mm.
- the value (G / d) of the ratio (G / d) of the diagonal length (G) of the mesh to the diameter (d) of the lead wire 301 is 1.2 or more, preferably 1.2 to. 33.
- a suitable example is 5 (0.5 mm / 0.1 mm).
- the lead wire 301 can be passed through the mesh of the braid 183 while avoiding contact with the metal wire bundle 181. If this value is less than 1.2, the lead wire cannot be passed through the braided mesh without contacting the metal wire bundle, or it becomes extremely difficult.
- the opening length (P) of the side hole 15 is 1.0 times or more the diameter (d) of the lead wire 301, 0.9 times or less the width (W) of the ring-shaped electrode 201, and the diagonal line of the mesh. It is preferable that the length (G) is 0.1 to 4.0 times.
- the opening length (P) of the side hole 15 is 1.0 times or more the diameter (d) of the lead wire 301, the insertion of the lead wire 301 into the side hole 15 can be ensured.
- the opening length (P) of the side hole 15 is 0.9 times or less the width (W) of the ring-shaped electrode 201, the opening of the side hole 15 can be reliably closed by the ring-shaped electrode 201.
- the opening length (P) of the side hole 15 is 0.1 times or more the diagonal length (G) of the mesh, contact with the metal wire bundle 181 existing in the side hole 15 is avoided.
- the lead wire 201 can be passed through the side hole 15. Since the opening length (P) of the side hole 15 is 4.0 times or less the diagonal length (G) of the mesh, the resin material (adhesive) to the side hole 15 at the time of manufacturing the electrode catheter 100 ) 16 filling operation can be easily performed.
- the diagonal length (G) of the mesh of the braid cannot be made sufficiently long, and the G / d value is set to 1.2 or more. It may not be possible to (pass the lead wire through the braided mesh).
- the entire length of the catheter shaft 10 is reinforced with a braid 183 formed by weaving a metal wire bundle 181. Therefore, the torque transmission property is excellent as compared with a conventionally known catheter. ing.
- the side hole 15 at the tip of the catheter shaft 100 is formed without cutting the metal wire bundle 181 (for example, when forming the side hole 15, without using a high-power laser device capable of cutting the metal wire bundle). ) Therefore, the side hole 15 can be easily formed.
- the length (G) of the diagonal line of the mesh of the braid 183 is 1.2 times or more the diameter (d) of the lead wires 301 to 310, so that the metal wire bundle 181 existing in the side hole 15 is formed.
- Each of the lead wires 301 to 310 can be passed through the mesh of the braid 183 while avoiding contact. As a result, it is possible to prevent the resin coating layer of the lead wires 301 to 310 from peeling off or the lead wires 301 to 310 from being broken during the manufacture of the electrode catheter 100. Further, since the resin material 16 is filled in the side hole 15 through which each of the lead wires 301 to 310 is inserted, the non-contact state between the lead wires 301 to 310 and the metal wire bundle 181 can be maintained. Therefore, even when the electrode catheter 100 is used (when the tip portion of the catheter shaft 10 is bent), the resin coating layer of the lead wires 301 to 310 may be peeled off or the lead wires 301 to 310 may be broken. Can be prevented.
- the catheter of the present invention is attached to a first DC electrode group composed of a plurality of ring-shaped electrodes attached to the tip end portion of the catheter shaft and to the tip end portion of the catheter shaft separated from the first DC electrode group toward the proximal end side.
- the second DC electrode group consisting of a plurality of ring-shaped electrodes, the first DC lead wire group consisting of lead wires connected to each of the electrodes constituting the first DC electrode group, and the electrodes constituting the second DC electrode group
- It may be a defibrillation catheter including a second DC lead wire group consisting of connected lead wires.
- the catheter of the present invention may be one in which the tip portion of the catheter shaft can be deflected, and the deflection direction may be one direction (single direction type) or two directions (bidirection type). ..
- the catheter shaft in the above embodiment has two lumens (guide wire lumen 11L and lumen 12L) formed by having a double tube structure, but the catheter shaft constituting the catheter of the present invention is at least. It may consist of a single multi-lumen tube with two lumens. It is also possible to construct the catheter of the present invention by a catheter shaft having a single lumen structure.
- Electrode catheter 10 Catheter shaft 101 Tip part 101A Tip side low hardness area 101B Hardness inclination area 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 Reinforcing layer 134 Resin 135 15 Side hole 16 Resin material (adhesive) 181 Metal wire bundle 183 Braided 201-210 Ring-shaped electrode 25 Tip tip 301-310 Lead wire 40 Handle 41 Connector 42 Guide wire port 51 Lead wire protection tube 52 Guide wire protection tube
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Abstract
Description
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。
また、このような構成のカテーテルは、編組の構成材料が切り替わる先端部分と基端部分の境界においてキンクが起こりやすい。
前記カテーテルシャフトは、その全長にわたる管壁に、金属素線または金属素線束で形成された編組が埋設されてなるブレードチューブであり、
前記カテーテルシャフトの先端部分における前記管壁には、前記リング状電極の装着位置に対応して、前記外周面から前記ルーメンに至る側孔が、前記金属素線または前記金属素線束を切断することなく形成され、
前記リード線は、その先端部が前記リング状電極の内周面に接合されることで当該リング状電極に接続されているとともに、前記側孔に挿通されることによって前記編組の網目を通過し、前記カテーテルシャフトの前記ルーメンに進入して当該ルーメンにおいて延在し、
前記リード線が挿通されている前記側孔には、樹脂材料が充填されており、
前記リード線の直径をd、前記編組の前記網目の、前記カテーテルシャフトの軸方向における対角線の長さをGとするとき、G/dの値が1.2以上であることを特徴とする。
また、カテーテルシャフトの管壁を貫通する側孔を、金属素線(束)を切断することなく形成することができるので、当該側孔を容易に形成することができる。
更に、編組の網目の対角線の長さ(G)がリード線の直径(d)の1.2倍以上であることにより、金属素線(束)が側孔内に存在していても、当該金属素線(束)との接触を避けて、編組の網目にリード線を通すことができる。これにより、当該カテーテルの製造時において、リード線の樹脂被覆層が剥離したり、当該リード線が断線したりすることを防止することができる。また、リード線が挿通されている側孔に樹脂材料が充填されてい
ることにより、リード線と金属素線(束)との非接触状態を維持することができるので、当該カテーテルの使用時(カテーテルシャフトの先端部分の曲げ操作時)においても、リード線における樹脂被覆層の剥離や断線を防止することができる。
G/dの値が1.2~33であることにより、リード線の樹脂被覆層が剥離したり当該リード線が断線したりするようなことを防止できるとともに、編組による補強効果を十分に確保することができる。
式(2):0.1≦P/G≦4.0
また、側孔の開口径(開口長さ)Pが0.9W以下であることにより、シャフト外周面における当該側孔の開口をリング状電極により確実に塞ぐことができる。
また、P/Gの値が4.0以下であることにより、製造時における側孔への樹脂材料の充填操作を容易に行うことができる。
また、径または幅が0.03~0.1mmの金属素線(束)によって編組が形成され、カテーテルシャフトの先端部分における当該編組の密度が265PPI以下であることにより、編組の網目の対角線の長さ(G)を十分に長くすることができ、G/dの値を確実に1.2以上とすること(編組の網目にリード線を通すこと)ができる。
図1~図6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リード線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の外周面とともにリード線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、外側チューブ13の管壁には、カテーテルシャフト10の全長にわたり、金属素線束181で形成された編組183が埋設されてなり、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、リング状電極201~210の装着位置に対応して、外周面からルーメン12Lに至る側孔15が、金属素線束181を切断することなく形成され、リード線301~310は、各々の先端部がリング状電極201~210の各々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に電気的に接続されているとともに、リング状電極201~210の装着位置に対応する側孔15に各々が挿通されることによって編組183の網目を通過し、側孔15からルーメン12Lに進入して当該ルーメン12Lに延在しており、リード線301~310の各々が挿通されている側孔15には、樹脂材料(接着剤)16が充填されており、リード線301~310の各々の直径をd、編組183の網目の、カテーテルシャフト10の軸方向における対角線の長さをGとするとき、G/dの値が1.2~33である。
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。
すなわち、外側チューブ13は、金属製の編組183により補強された樹脂チューブであるブレードチューブからなる。
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。
なお、外側チューブ13を補強する編組の打ち数および持ち数は適宜変更することができる。ここに、打ち数としては8~32であることが好ましく、編組の持ち数としては1~4であることが好ましい。
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。
また、金属素線束181を構成する金属素線の線径(W181/持ち数)としては、通常0.02~0.1mmとされ、好適な一例を示せば0.06mm(0.12mm/2)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。
造することができる。
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。
なお、図4においては、外側チューブ13の管壁に埋設されている編組(金属素線束)の図示を省略しているが、リード線301と金属素線束とは接触していない。
また、リング状電極202~210の内周面にそれぞれ接合されているリード線302~310についても、図4に示した形態と同様である。
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。
ネクタ41に内蔵されている複数の端子の各々に接続されている。
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。
なお、リング状電極202~210の内周面にそれぞれ接合されているリード線302~310についても、図6に示した形態と同様である。
ここに、編組183の網目の対角線の長さ(G)としては0.07~1.3mmであることが好ましく、好適な一例を示せば0.3mmである。
ここに、カテーテルシャフト10の軸方向における側孔15の開口長さ(P)としては0.04~9.9mmであることが好ましく、好適な一例を示せば0.5mmである。
この値が1.2未満であると、金属素線束と接触させずにリード線を編組の網目に通過させることができないか、きわめて困難となる。
この値が過大であると、そのような編組によっては十分な補強効果を発揮することができない。
側孔15の開口長さ(P)が、リング状電極201の幅(W)の0.9倍以下であることにより、側孔15の開口をリング状電極201により確実に塞ぐことができる。
側孔15の開口長さ(P)が、網目の対角線の長さ(G)の4.0倍以下であることにより、電極カテーテル100の製造時において、側孔15への樹脂材料(接着剤)16の充填操作を容易に行うことができる。
他方、編組の密度が265を超える(過密)である編組によっては、編組の網目の対角線の長さ(G)を十分に長くすることができず、G/dの値を1.2以上とする(編組の網目にリード線を通す)ことができなくなることがある。
また、カテーテルシャフト100の先端部分における側孔15を、金属素線束181を切断することなく(例えば、側孔15の形成に際して、金属素線束を切断可能な高出力のレーザ装置を使用することなく)形成することができるので、当該側孔15を容易に形成することができる。
さらに、編組183の網目の対角線の長さ(G)が、リード線301~310の直径(d)の1.2倍以上であることにより、側孔15内に存在する金属素線束181との接触を避けながら編組183の網目にリード線301~310の各々を通すことができる。
これにより、電極カテーテル100の製造時において、リード線301~310の樹脂被覆層が剥離したり、当該リード線301~310が断線したりすることを防止することができる。また、リード線301~310の各々が挿通されている側孔15に樹脂材料16が充填されていることにより、リード線301~310と金属素線束181との非接触状態を維持することができるので、電極カテーテル100の使用時(カテーテルシャフト10の先端部分の曲げ操作時)においても、リード線301~310の樹脂被覆層が剥離したり、当該リード線301~310が断線したりすることを防止することができる。
例えば、本発明のカテーテルは、カテーテルシャフトの先端部分に装着された複数のリング状電極からなる第1DC電極群と、第1DC電極群から基端側に離間してカテーテルシャフトの先端部分に装着された複数のリング状電極からなる第2DC電極群と、第1DC電極群を構成する電極の各々に接続されたリード線からなる第1DCリード線群と、第2DC電極群を構成する電極の各々に接続されたリード線からなる第2DCリード線群とを備えてなる除細動カテーテルであってもよい。
また、本発明のカテーテルは、カテーテルシャフトの先端部分を偏向操作可能にしたものでもよく、その偏向方向は1方向(シングルディレクションタイプ)であっても2方向(バイディレクションタイプ)であってもよい。
また、上記の実施形態におけるカテーテルシャフトは、二重管構造とすることで2つの
ルーメン(ガイドワイヤルーメン11L及びルーメン12L)を形成しているが、本発明のカテーテルを構成するカテーテルシャフトは、少なくとも2つのルーメンを有する1本のマルチルーメンチューブからなるものであってもよい。また、シングルルーメン構造のカテーテルシャフトにより本発明のカテーテルを構成することも可能である。
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
16 樹脂材料(接着剤)
181 金属素線束
183 編組
201~210 リング状電極
25 先端チップ
301~310 リード線
40 ハンドル
41 コネクタ
42 ガイドワイヤポート
51 リード線保護チューブ
52 ガイドワイヤ保護チューブ
Claims (4)
- 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、金属芯線を樹脂被覆してなり、前記リング状電極に接続されたリード線とを備えてなるカテーテルにおいて、
前記カテーテルシャフトは、その全長にわたる管壁に、金属素線または金属素線束で形成された編組が埋設されてなるブレードチューブであり、
前記カテーテルシャフトの先端部分における前記管壁には、前記リング状電極の装着位置に対応して、前記外周面から前記ルーメンに至る側孔が、前記金属素線または前記金属素線束を切断することなく形成され、
前記リード線は、その先端部が前記リング状電極の内周面に接合されることで当該リング状電極に接続されているとともに、前記側孔に挿通されることによって前記編組の網目を通過し、前記カテーテルシャフトの前記ルーメンに進入して当該ルーメンにおいて延在し、
前記リード線が挿通されている前記側孔には、樹脂材料が充填されており、
前記リード線の直径をd、前記編組の前記網目の、前記カテーテルシャフトの軸方向における対角線の長さをGとするとき、G/dの値が1.2以上であることを特徴とするカテーテル。 - G/dの値が1.2~33であることを特徴とする請求項1に記載のカテーテル。
- 前記側孔の開口径または前記カテーテルシャフトの軸方向における前記側孔の開口長さをPとし、前記側孔の形成位置に装着された前記リング状電極の電極幅をWとするとき、下記式(1)および(2)が成立することを特徴とする請求項1または2に記載のカテーテル。
式(1):1.0d≦P≦0.9W
式(2):0.1≦P/G≦4.0 - 前記金属素線の径もしくは幅または前記金属素線束の幅が0.03~0.1mmであり、少なくとも前記カテーテルシャフトの先端部分における前記編組の密度が13~265PPIであることを特徴とする請求項1~3の何れかに記載のカテーテル。
Priority Applications (6)
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JP2021508443A JP7210699B2 (ja) | 2019-03-25 | 2019-03-25 | カテーテル |
PCT/JP2019/012621 WO2020194474A1 (ja) | 2019-03-25 | 2019-03-25 | カテーテル |
EP19920877.8A EP3949844B1 (en) | 2019-03-25 | 2019-03-25 | Catheter |
CN201980085473.7A CN113271855B (zh) | 2019-03-25 | 2019-03-25 | 导管 |
KR1020217019646A KR20210095188A (ko) | 2019-03-25 | 2019-03-25 | 카테터 |
US17/408,432 US20210378573A1 (en) | 2019-03-25 | 2021-08-22 | Catheter |
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PCT/JP2019/012621 WO2020194474A1 (ja) | 2019-03-25 | 2019-03-25 | カテーテル |
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US17/408,432 Continuation US20210378573A1 (en) | 2019-03-25 | 2021-08-22 | Catheter |
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WO2020194474A1 true WO2020194474A1 (ja) | 2020-10-01 |
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US (1) | US20210378573A1 (ja) |
EP (1) | EP3949844B1 (ja) |
JP (1) | JP7210699B2 (ja) |
KR (1) | KR20210095188A (ja) |
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CN216456448U (zh) * | 2021-09-26 | 2022-05-10 | 惠州海卓科赛医疗有限公司 | 一种医用管 |
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JP2012034852A (ja) | 2010-08-06 | 2012-02-23 | Japan Lifeline Co Ltd | 電極カテーテル |
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CN102139136B (zh) * | 2011-03-11 | 2013-07-17 | 上海微创医疗器械(集团)有限公司 | 一种球囊扩张导管 |
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2019
- 2019-03-25 JP JP2021508443A patent/JP7210699B2/ja active Active
- 2019-03-25 WO PCT/JP2019/012621 patent/WO2020194474A1/ja unknown
- 2019-03-25 KR KR1020217019646A patent/KR20210095188A/ko not_active Application Discontinuation
- 2019-03-25 EP EP19920877.8A patent/EP3949844B1/en active Active
- 2019-03-25 CN CN201980085473.7A patent/CN113271855B/zh active Active
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JP2013123508A (ja) | 2011-12-14 | 2013-06-24 | Japan Lifeline Co Ltd | 先端偏向操作可能カテーテル |
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JP2017148472A (ja) | 2016-02-25 | 2017-08-31 | 日本ライフライン株式会社 | 電極カテーテル |
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US20210378573A1 (en) | 2021-12-09 |
CN113271855A (zh) | 2021-08-17 |
EP3949844A4 (en) | 2022-10-26 |
EP3949844B1 (en) | 2023-09-13 |
KR20210095188A (ko) | 2021-07-30 |
JP7210699B2 (ja) | 2023-01-23 |
CN113271855B (zh) | 2023-07-14 |
EP3949844A1 (en) | 2022-02-09 |
JPWO2020194474A1 (ja) | 2021-10-28 |
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