WO2006109649A1 - カテーテル - Google Patents
カテーテル Download PDFInfo
- Publication number
- WO2006109649A1 WO2006109649A1 PCT/JP2006/307228 JP2006307228W WO2006109649A1 WO 2006109649 A1 WO2006109649 A1 WO 2006109649A1 JP 2006307228 W JP2006307228 W JP 2006307228W WO 2006109649 A1 WO2006109649 A1 WO 2006109649A1
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- WIPO (PCT)
- Prior art keywords
- shaft
- catheter
- distal
- inner shaft
- lumen
- Prior art date
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Classifications
-
- 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
- A61M25/0029—Multi-lumen catheters with stationary elements characterized by features relating to least one lumen located at the middle part of the catheter, e.g. slots, flaps, valves, cuffs, apertures, notches, grooves or rapid exchange ports
-
- 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
-
- 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
- A61M25/0032—Multi-lumen catheters with stationary elements characterized by at least one unconventionally shaped lumen, e.g. polygons, ellipsoids, wedges or shapes comprising concave and convex parts
-
- 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
- A61M25/10—Balloon catheters
-
- 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
- A61M2025/0037—Multi-lumen catheters with stationary elements characterized by lumina being arranged side-by-side
-
- 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
- A61M2025/0183—Rapid exchange or monorail catheters
Definitions
- the present invention relates to a catheter used for medical use, and more specifically, percutaneous angioplasty (PTA: Percuta neous Transluminal Angioplasty, when performing peripheral angioplasty, coronary artery formation, valvuloplasty, etc.
- PTA Percuta neous Transluminal Angioplasty
- PTCA Percutaneous Transluminal Coronary Angioplasty
- percutaneous angioplasty has been widely used for the purpose of expanding or treating stenosis or occlusion in the lumen of blood vessels and restoring or improving blood flow in coronary arteries and peripheral blood vessels.
- a balloon catheter used for percutaneous angioplasty is formed by joining an inflatable / contractable lane by adjusting the internal pressure to the tip of the shaft, and a guide wire is inserted into the shaft.
- a structure in which a lumen (guide wire lumen) and a lumen (inflation lumen) for supplying pressure fluid for adjusting balloon internal pressure are provided along the longitudinal direction of the shaft.
- a general operation example of PTCA using such a balloon catheter is as follows. First, the guide catheter is inserted into the puncture site force of the femoral artery, brachial artery, radial artery, etc., and the distal end is placed at the entrance of the coronary artery via the aorta. Next, the guide wire passed through the guide wire lumen is advanced beyond the stenosis site of the coronary artery, and a balloon catheter is inserted along the guide wire so that the balloon matches the stenosis. Next, using a device such as an inflator, a pressure fluid is supplied to the balloon via the inflation lumen, and the balloon is inflated to expand the stenosis. After dilatation of the stenosis, PTCA is completed by decompressing the balloon and removing it from the body.
- the degree of stenosis is very high.
- the guide wire cannot be advanced and treatment cannot be performed.
- a penetrating catheter is used to achieve advancement of the guide wire across the stenotic site.
- PTCA local administration of a therapeutic substance to the stenotic site may be required.
- An example is treatment in which a thrombolytic agent such as urokinase is locally administered to dissolve the thrombus.
- an infusion catheter that administers the therapeutic substance locally is used.
- Each of the catheters described above has a structure in which a distal shaft and a proximal shaft are joined, and a catheter holding hub is connected to the proximal end of the proximal shaft. It is roughly classified into two according to the length of. Below, a balloon is connected to the distal side of the distal shaft, and a balloon catheter equipped with a port for supplying pressure fluid for adjusting the internal pressure of the balloon to the inflation lumen will be described as an example (Figs. 1 and 2). .
- a guide wire lumen is provided over the entire length of the catheter as shown in FIG. 1.
- a proximal end side opening 1B of the guide wire lumen and an opening 2A of the inflation lumen are provided in the hub 3.
- a strain relief 4 for controlling the axial flexibility is provided on the hub 3, and the guide wire is located more distal than the most distal end of the balloon 5 or the most distal end of the lane 5.
- the over-the-wire type (OTW type) is provided with a lumen opening 1 A at the distal end of the lumen. As shown in Fig.
- the guide wire lumen exists only on the distal side of the balloon catheter, and the proximal end opening 1B of the guide wire lumen is provided in the middle of the distal shaft 6 as shown in Fig. 2.
- High-speed exchange type RX type
- the OTW type Since the OTW type has a guide wire lumen over the entire length of the balloon catheter, it is often used for lesions where it is difficult to pass the guide wire.
- the balloon catheter is removed while the guide catheter remains in the lesion. There is a problem that the work to do is complicated. In other words, in the OTW type, special devices and operations such as attaching replacement extension wires are required to remove the catheter while leaving the guide wire in place in the affected area.
- the balloon catheter can be easily removed, replaced, and reinserted while the guide wire is left in the lesion. Not only is the operability very good, but also the operation time is shortened. It is possible to reduce the number of devices used.
- the balloon catheter provided with a balloon on the distal side of the distal shaft has been described above, the features of the OTW type and the RX type are not limited to the non-lane catheter, and the penetration for stenosis penetration is performed. The same applies to catheters, infusion catheters for therapeutic substance administration, and other catheters.
- the structure of the catheter is roughly classified into two according to the shaft structure where the guide wire lumen exists.
- One is a guide wire lumen 1 in which an inner shaft 8 and an outer shaft 9 are disposed so as to coaxially surround the inner shaft 8 as shown in a cross-sectional shape in FIG.
- a coaxial type co-axial type having a second lumen (“2” in FIG. 4) having an annular cross section formed between the inner shaft 8 and the outer shaft 9.
- the second lumen is an inflation lumen
- the catheter is an infusion catheter
- the second lumen is an infusion lumen.
- the other is a bi-axial structure (not shown) with a guidewire lumen and a second lumen aligned in parallel.
- the biaxial type when the catheter is a balloon catheter, the second lumen is an inflation lumen, and when the catheter is an infusion catheter, the second lumen is an infusion lumen.
- a coaxial type or a biaxial type structure is generally provided over the entire length.
- the distal shaft in the portion where the guide carrier lumen exists can have a coaxial type or a biaxial type structure.
- Patent Document 1 a first tube member that forms a guide wire lumen, and an outer surface that extends in the same direction as the first tube member and is coupled to the outer peripheral surface of the first tube member.
- An over-the-wire catheter having a second tube member that forms an inflation lumen, a balloon, and means for changing the flexibility of at least one of the first and second tube members is disclosed.
- the constituent members of the catheter including the first and second tube members and the member for controlling flexibility are individually selected. This makes it possible to select the performance characteristics of the catheter and maintain good performance characteristics.
- the manufacturing method is easy, the cost can be kept low.
- an adhesive or a sleeve member is used for joining the first and second tube members, the large diameter and flexibility of the joint portion are reduced, and the operability of inserting into a bent blood vessel is high. However, it was powerful.
- Patent Document 2 an inner tubular member, an outer tubular member, and an elongated force tape that is an expansion balloon force, a second lumen is formed between the inner tubular member and the outer tubular member, and the expansion balloon is formed. Is in communication with the second lumen and has an adhesive longitudinal portion of the inner tubular member and the outer tubular member, the adhesive longitudinal portion occupies at least 30% of the inner peripheral surface of the outer tubular member, and the inner tubular member A catheter having an inner peripheral surface bonded to the outer surface of the catheter is disclosed.
- the outer diameter of the catheter body can be reduced at least in one direction in this region, and the diameter can be reduced. Is done. Furthermore, since the adhesion part of an inner tubular member and an outer tubular member mutually supports, the pressability of a catheter is improved. However, since the inner tubular member and the outer tubular member are bonded to each other at the bonded long portion, the flexibility is lowered, and the operability when the bonded long portion passes through the bent blood vessel is not good. Further, in the state in which the adhesive longitudinal portion is bent, the second lumen included in the adhesive longitudinal portion is easily deformed, and there is a problem that the expansion / contraction response of the dilatation balloon is low.
- Patent Document 3 an elongated catheter having a balloon, in which the shaft of the catheter is formed with an inner tube and an outer tube force surrounding the inner tube, and an expansion lumen is formed between them.
- a coaxial balloon inflation catheter is disclosed that is attached to the outer tube where the inner tube is distal to the proximal end of the shaft.
- Patent Document 1 Japanese Patent No. 3583460
- Patent Document 2 Japanese Patent No. 3399556
- Patent Document 3 Japanese Patent No. 2960114
- the present invention intends to solve the problem where a shaft structure where the guide wire lumen is present is a coaxial structure, and is added to the proximal side of the catheter. It has pushability that can efficiently transmit force to the distal side or distal end of the catheter, and suppresses the inner shaft and outer shaft that form the coaxial structure from being nested together. This makes it possible to achieve a catheter with improved permeability to the stenosis without compromising the flexibility of the catheter, and at the same time, dilatation of the balloon in the case of a balloon catheter, and infusion responsiveness in the case of an infusion catheter. There is no catheter to realize.
- a catheter which is a proximal shaft and a distal shaft, each having a proximal end portion and a distal end portion.
- the proximal end of the proximal shaft and the proximal end of the distal shaft are joined to each other, and the catheter holding hub is attached to the proximal end of the proximal shaft.
- At least a portion of the distal shaft is formed from an inner shaft and an outer shaft that coaxially surrounds the inner shaft, the inner shaft being distal to the outer shaft.
- the inner shaft lumen forms a guide wire lumen, and the outer shaft and the inner shaft move relative to each other when a certain pushing force is applied to the catheter.
- the present inventors have invented a catheter characterized in that means for suppressing this is provided.
- the means is composed of a protrusion provided on the outer surface of the inner shaft and a reduced diameter portion provided on the inner surface of the outer shaft.
- the protrusion is more distal than the reduced diameter portion. More preferably, it is arranged on the side.
- a catheter according to the present invention includes a foldable balloon having a proximal end and a distal end, and the proximal end is joined to a distal region of the outer shaft.
- the distal end portion is joined to a distal region of the inner shaft, and an inflation lumen having an annular cross-section is formed between the inner shaft and the outer shaft;
- the inflation lumen may communicate with the inside of the balloon, and the projection portion stops against the reduced diameter portion, so that the outer shaft and the inner shaft are prevented from relatively moving. It is preferable that the inflation lumen is secured in the corresponding stop portion in the state of being.
- the catheter according to the present invention is a penetration catheter for penetrating a body cavity constriction, and the distal region of the inner shaft and the distal region of the outer shaft are joined.
- the catheter according to the present invention is an infusion catheter capable of administering a therapeutic substance to a local site of a body cavity, wherein a distal region of the inner shaft and a distal region of the outer shaft are joined.
- An infusion lumen having an annular cross section is formed between the inner shaft and the outer shaft, and the outer shaft may have an injection hole. It is preferable that the infusion lumen is secured in the corresponding stop portion in a state where the reduced diameter portion is stopped and the outer shaft and the inner shaft are restrained from relatively moving. .
- the invention's effect in a catheter in which the shaft structure where the guide wire lumen exists is a coaxial structure, the force applied to the catheter proximal side is efficiently transmitted to the catheter distal side or distal end.
- the catheter is designed to be able to pass through the stenosis by suppressing the inner shaft and the outer shaft that form a coaxial structure from being nested with each other.
- a balloon catheter it is possible to realize a balloon expansion / contraction response, and in the case of an injection catheter, to achieve a catheter that does not impair the injection response.
- FIG. 1 is a schematic perspective view of an over-the-wire type (OTW type) among general balloon catheters.
- OGW type over-the-wire type
- FIG. 2 is a schematic perspective view of a high-speed exchange type (RX type) among general balloon catheters.
- FIG. 3 is a partial schematic side view showing a longitudinal section of a distal portion of a catheter having a guide wire lumen partial force S coaxial structure in a general RX balloon catheter.
- FIG. 4 is a cross-sectional view taken along the line AA ′ of FIG.
- FIG. 5 is a partial schematic side view showing a longitudinal section when a balloon is deformed in an accordion shape in a general RX type balloon catheter.
- FIG. 6 is a partial schematic side view showing a longitudinal section of a balloon catheter according to the present invention.
- FIG. 7 is an example of a BB ′ sectional view of FIG.
- FIG. 8 is an example of a cross-sectional view taken along the line BB ′ of FIG.
- FIG. 9 is an example of a cross-sectional view taken along the line BB ′ of FIG.
- FIG. 10 is an example of a BB ′ sectional view of FIG.
- FIG. 11 is an example of a cross-sectional view along CC ′ in FIG.
- FIG. 12 is an example of a cross-sectional view along CC ′ in FIG.
- FIG. 13 is an example of a cross-sectional view along CC ′ in FIG.
- FIG. 14 is an example of a cross-sectional view along CC ′ in FIG.
- FIG. 15 is an example of a cross-sectional view along CC ′ in FIG.
- FIG. 16 is an example of a cross-sectional view of CC ′ of FIG.
- FIG. 17 is an example of a cross-sectional view along CC ′ in FIG.
- FIG. 18 is a partial schematic side view showing a longitudinal section in a state in which the protruding portion 12 and the reduced diameter portion 13 shown in FIG. 6 are in contact with each other.
- FIG. 19 is a partial schematic side view showing a longitudinal section of an infusion catheter according to the present invention.
- FIG. 20 is a partial schematic side view showing a longitudinal section of a penetration catheter according to the present invention.
- FIG. 21 is a schematic perspective view showing an example of a core material used for processing an example of the reduced diameter portion according to the present invention.
- FIG. 22 is a schematic perspective view showing another example of the core material used for processing an example of the reduced diameter portion according to the present invention.
- FIG. 23 is a schematic diagram showing a catheter evaluation system according to the present invention.
- the catheter according to the present invention has a proximal shaft and a distal shaft each having a proximal end and a distal end, and the distal end of the proximal shaft and the distal shaft Distal shuff A proximal end of the proximal shaft and a proximal end of the proximal shaft to which the catheter holding hub is joined. At least a part of the distal shaft is connected to the inner shaft and the inner shaft.
- the inner shaft extends distally beyond the outer shaft, and the inner shaft lumen forms a guide wire lumen. If it is a coaxial type, the structure beyond it is not particularly limited. In other words, the OTW type shown in FIG. 1 or the RX type shown in FIG. 2 may be used. Further, other structures may be used.
- the cross section AA ′ of the coaxial type portion has a structure as shown in FIG.
- the catheter as shown in Fig. 3 it is necessary to apply force to the knob provided at the proximal end of the proximal shaft and push the catheter forward.
- the degree of bending to the treatment site is high! In some cases, such as when the treatment site has a high degree of stenosis, the catheter cannot be pushed forward easily, so that a greater force can be obtained.
- the inner shaft 8 and the outer shaft 9 constituting at least a part of the distal shaft are fitted in a nested manner, and as a result, the balloon 5 portion is arranged as shown in FIG. It can be transformed into one dion. Such deformation increases the outer diameter of the balloon 5 and makes it more difficult to place it at the treatment site.
- the balloon part is accordion-shaped as described above.
- the inner shaft and the outer shaft are fitted in a telescopic manner, it is difficult to sufficiently transmit the force to the catheter tip. Therefore, it is not easy to place these catheters at the treatment site.
- the catheter according to the present invention is provided with means for suppressing relative movement of the outer shaft and the inner shaft when a pushing force of a certain level or more is applied to the catheter. It is characterized by that. Occurrence of the phenomenon in which the outer shaft and the inner shaft fit in a nested manner is effectively suppressed by the means, and the balloon portion is deformed into an accordion shape. At the same time, the power raised in the hub It can be effectively transmitted to the catheter tip, and the placement operability at the treatment site is improved.
- the structure of the means is provided on the outer surface of the inner shaft 8 as shown in FIG. 6 in consideration of the flexibility of the portion including the means and the stability of the process including the means. It is preferable that the projection portion 12 and the reduced diameter portion 13 provided on the inner surface of the outer shaft 9 are configured. By configuring the means from the projecting portion 12 and the reduced diameter portion 13, when a force is applied to the catheter, the projecting portion 12 and the reduced diameter portion 13 stop as shown in FIG. The outer shaft 9 and the inner shaft 8 no longer fit in a nested manner. A suitable structure of the portion where the reduced diameter portion 13 and the protruding portion 12 come into contact will be described later. Any structure is included.
- protruding part stopping against the reduced diameter part is that when the protruding part and the reduced diameter part are in contact, or when the protruding part and Z or the reduced diameter part are buffered (both parts (or either On the other hand, including the state where the inflation lumen is deformed to the extent that it is not completely closed at the time of force contact), the case where the protrusion and the reduced diameter portion are fitted is also included.
- the arrangement of the protruding portion 12 and the reduced diameter portion 13 cannot be generally limited depending on the outer shaft, the type of the resin constituting the inner shaft, the structure of the catheter, and the like.
- the inner shaft is more pressured than the outer shaft, and if the inner shaft is easily moved as a result, the protrusion 12 is disposed more distally than the reduced diameter portion 13. It is preferable (for example, FIGS. 6, 19, and 20). This place
- by disposing the protrusion 12 on the distal side when a pushing force greater than a certain level is applied to the catheter, the protrusion 12 is relatively proximal as shown in FIG. It moves, and the stop with the said reduced diameter part 13 is implement
- the positions of the protrusion and the reduced diameter portion are set according to the type of catheter and the target treatment site.
- the position of the protrusion and the reduced diameter portion does not impair the flexibility of the balloon catheter. I prefer it as close as possible.
- the expandable portion proximal end corresponds to the proximal end of the proximal tapered portion 5C shown in FIG.
- the distance can be set in consideration of the material constituting the inner shaft and the outer shaft, the dimensions of the inner shaft and the outer shaft, the pushing force that can be applied to the force taper, and the like.
- the distance is preferably 5. Omm or less.
- the distance is greater than 5. Omm, the noren part is deformed into an accordion shape before the protrusion and the reduced diameter part come into contact.
- the reduced diameter portion is disposed on the distal side of the protrusion, the distance between the proximal end of the reduced diameter portion and the distal end of the protrusion that contacts at the time of stopping is the same. It is.
- the lengths of the protrusions and the reduced diameter portions in the shaft axial direction are the materials constituting the inner shaft and the outer shaft, the dimensions of the inner shaft and the outer shaft, the pushing force that can be applied to the force tail, and the like. It can be set in consideration. If the length of the protrusion and the reduced diameter portion is too long, the flexibility of the catheter is lowered, which is not preferable. On the other hand, if the lengths of the projection and the reduced diameter portion are too short, the projection portion stops against the reduced diameter portion, and then passes through the reduced diameter portion to the proximal side of the reduced diameter portion. Move nested This is not preferable because of the possibility.
- the length of the protrusion is preferably 0.5 mm or more and 3. Omm or less. 1. Omm or more, 2. Omm
- the length of the reduced diameter portion is more preferably 0.5 mm or more and 7. Omm or less, more preferably 2. Omm or more and 5. Omm or less.
- a catheter according to the present invention includes a foldable balloon having a proximal end and a distal end, and the proximal end is joined to a distal region of the outer shaft.
- the distal end is joined to a distal region of the inner shaft, and forms an inflation lumen having an annular cross section between the inner shaft and the outer shaft;
- the lumen may be a balloon catheter communicating with the inside of the balloon.
- the protruding portion 12 comes into contact with the reduced diameter portion 13, and the outer shaft 9 and the inner shaft 8 are restrained from relatively moving.
- the inflation lumen 2 is secured at the corresponding stop portion.
- the stopper portion refers to a portion where the protrusion 12 and the reduced diameter portion 13 are stopped (hereinafter the same).
- the inflation lumen 2 is secured when the inflation lumen 2 is completely blocked by the stop portion.
- the catheter according to the present invention is an infusion catheter capable of administering a therapeutic substance to a local site of a body cavity as shown in FIG. 19, and includes a distal region of the inner shaft 8 and the outer shaft 9.
- An infusion lumen 10 having an annular cross section formed between the inner shaft 8 and the outer shaft 9 and having an injection hole 16 in the outer shaft 9. It does not matter.
- infusion lumen 10 is secured! The fact that the infusion lumen is secured means that the infusion lumen is not completely closed at the stop.
- the protrusion 12 and the reduced diameter portion 13 are stopped by the pushing force applied to the catheter. Even so, the therapeutic substance can be administered to the treatment site.
- a specific structure of the protrusion and the reduced diameter portion will be described later.
- the catheter according to the present invention is a penetration force taper for penetrating a body cavity stenosis as shown in FIG. 20, and includes a distal region of the inner shaft 8 and a distal region of the outer shaft 9. It may be a penetrating catheter that is joined together.
- the protruding portion 12 abuts on the reduced diameter portion 13, In the state where the outer shaft 9 and the inner shaft 8 are restrained from moving relative to each other, it is not necessary to secure the lumen at the corresponding stop portion.
- the structure of the protrusion 12 provided on the inner shaft 8 and the reduced diameter portion 13 provided on the outer shaft 9 is the same as that of the outer shaft 9 and the structure shown in FIG. Any structure that can be stopped so as not to be nested when the inner shaft 8 moves relatively may be used. Further, as described above, when the catheter is a balloon catheter or an infusion catheter (FIGS. 6 and 19), the inflation lumen 2 or the infusion lumen with the projection 12 and the reduced diameter portion 13 stopped. It is preferable that 10 is secured. When the catheter is a penetrating catheter (FIG. 20), a structure in which the second lumen 17 is secured with the protrusion 12 and the diameter-reduced portion 13 being in contact with each other or a well-structured heel structure is acceptable.
- FIG. 7 to FIG. correspond to the BB ′ cross section in FIG.
- the outer shape of the inner shaft 8 is a hexagon, and in FIG. 8, the inner diameter of the inner shaft 8 is maintained.
- four fins 14 are provided on the outer surface of the inner shaft 8, and in FIG. 10, the tubular member 15 is connected to the outer surface of the inner shaft 8.
- the protrusion 12 is formed by providing a portion larger than the outer diameter of the tubular inner shaft 8 to the extent that it can come into contact with the tube 13. For example, in FIGS.
- the protrusion 12 in FIG. 9 and the tubular member 15 in FIG. are suitable examples, and various shapes can be used as long as the contact with the reduced diameter portion 13 can be realized.
- the shape of the protrusion is reduced (for example, when the fin shown in FIG. 9 is provided), the area of the inflation lumen or infusion lumen can be secured, and the flow of liquid in these lumens can be improved.
- the shape of the inflation lumen 2 is a combination of a semicircular shape, a square shape and a circular shape, or a gear shape. 13 is formed.
- the liquid flow rate in the inflation lumen 2 can be maintained at a suitable level even when the projection 12 is stopped.
- the inflation lumen 2 is secured by the two semicircular portions 2a 'and the quadrangular portion 2a ".
- the inflation lumen 2 is obtained by the semicircular portion 2a', which is the tooth portion. Is secured.
- the annular lumen 2a and the inflation lumen 2b that surround the inner shaft 8 are made independent, and the shape and quantity of the inflation lumen 2b are changed to reduce the size.
- a diameter portion 13 is formed.
- the liquid flow rate can be maintained at a suitable level by the inflation lumen 2b.
- the shape and quantity of the inflation lumen 2b are two circles in FIG. 12, eight circles in FIG. 14, one round force in FIG. 15, one rectangle in FIG. 16, and two circles in FIG. In both cases, the contact with the projection 1 2 is realized, and even when the contact is stopped, the inflation lumens 2a and 2b are connected to each other. Making it possible Thus, the inflation lumen 2 is secured.
- FIGS. 11 to 17 are a means for suppressing relative movement of the inner shaft and the outer shaft.
- the structures shown in FIGS. 11 to 17 can be suitably used.
- a ridge structure that does not have an inflation lumen (in the case of a balloon catheter) or an infusion lumen (in the case of an infusion catheter). Can be used.
- a method of providing the protrusion on the outer surface of the inner shaft is not particularly limited.
- a method of connecting the tubular member 15 to the outer surface of the inner shaft 8 having a circular cross section as shown in FIG. 10 a tube having a cross section corresponding to the inner shaft 8 as shown in FIGS.
- the cross-sectional shape shown in Fig. 8 can be formed by connecting a tube with one end expanded to another tube.
- the method for providing the reduced diameter portion on the outer shaft is not particularly limited.
- the cross-sectional shape of the inflation lumen 2 is changed as shown in FIG. 11 or FIG. 13, for example, the core materials 26A and 26B as shown in FIG. 21 and FIG. 22 are inserted into the outer shaft and heated.
- a method of giving the above-mentioned shape to the lumen can be used.
- the desired cross-sectional shape can be obtained by extrusion or the like.
- a tube having a shape may be made and the tube connected to the outer shaft.
- a method of connecting a different tube or the like to the inner shaft or the outer shaft when providing the protruding portion or the reduced diameter portion a combination of materials that can be bonded and fused with an adhesive is used. Methods such as wearing can be used.
- the composition, chemical structure, and curing type of the adhesive are not limited. In other words, urethane type, silicone type, epoxy type, cyanoacrylate type and other adhesives are preferably used in terms of composition and chemical structure, and in terms of curing type, two-component mixed type, UV curable type. Adhesives such as water-absorbing curing type and heat curing type are preferably used.
- Adhesive is used in consideration of dimensions, rigidity, etc. It is possible to select.
- the connection site is plasma treated with oxygen gas or the like to improve adhesion. You may adhere
- a core material having an arbitrary size may be inserted into the tube for the outer shaft.
- the force includes the core materials 26A and 26B shown in FIGS. 21 and 22.
- the present invention is not limited to these.
- the outer surface of the core material is coated with a fluorine-based resin such as polytetrafluoroethylene, polyparaxylylene, polymonochloro-opened paraxylylene, or the like. It is preferable that the core material be easily removed.
- the dimensions, cross-sectional shape, and the like of the core material to be used can be determined in consideration of the cross-sectional area of the required lumen, etc. as well as workability during processing that does not limit the effects of the present invention.
- the material constituting the distal shaft that is, the protrusion provided on the inner shaft and the inner shaft, and the reduced diameter portion provided on the outer shaft and the outer shaft are not particularly limited.
- the inner shaft (or outer shaft) and the protrusion (or reduced diameter portion) may be made of the same material or different materials.
- Polyolefin, polyolefin elastomer, polyester, polyester elastomer, polyamide, polyamide elastomer, polyurethane, polyurethane elastomer, etc. can be used as the material for the inner shaft or protrusion.
- the inner shaft lumen forms a guide wire lumen
- at least a part of the inner shaft which is preferably polyethylene, especially high-density polyethylene, has a multilayer structure, and is the innermost layer. It is more preferable that the material is made of high density polyethylene and the outermost layer is made of a material that can be melted with a balloon or an outer shaft.
- the present invention can be easily realized by using the multi-layer structure portion as a protrusion.
- the inner shaft lumen may be coated with polydimethylsiloxane or the like.
- the material of the outer shaft or the reduced diameter portion is not particularly limited. That is, polyolefins, polyolefin elastomers, polyesters, polyester elastomers, polyamides, polyamide elastomers, polyurethanes, polyurethane elastomers, and the like can be used.
- the material of the proximal shaft is not particularly limited, but the material of the proximal shaft is far away. It is preferable that the rigidity is substantially equal to or higher than that of the distal shaft. Furthermore, from the viewpoint of workability, safety to living bodies, etc., it is preferable to use a high-rigidity resin material such as a metal such as stainless steel, polyimide, polyamideimide, or polyetheretherketone.
- a high-rigidity resin material such as a metal such as stainless steel, polyimide, polyamideimide, or polyetheretherketone.
- the distal end of the proximal shaft is formed by forming a spiral cut, groove, slit, or the like on the distal side of the proximal shaft. You may reduce the side stiffness compared to the proximal side of the proximal shaft.
- the catheter is an injection catheter
- the size, position, number, etc. of the injection hole 16 can be arbitrarily set according to the characteristics of the therapeutic substance to be used.
- the method for producing the injection hole 16 is not particularly limited, and cutting and laser processing can be used, and the type of laser to be used is not particularly limited.
- the catheter is a balloon catheter
- a balloon molding method for producing a balloon by blow molding is shown below.
- a tube-shaped parison of arbitrary dimensions is formed by extrusion molding or the like.
- the tubular parison is placed in a mold having a mold that matches the balloon shape, and stretched in the axial direction and the radial direction by a biaxial stretching process, thereby forming a balloon having the same shape as the mold.
- the biaxial stretching step may be performed under heating conditions or may be performed a plurality of times. Further, the axial stretching may be performed simultaneously with or before or after the radial stretching. Further, annealing may be performed to stabilize the shape and dimensions of the balloon.
- nolane is connected to the straight pipe portion 5A and its distal and proximal joints.
- the size of the balloon is determined by the intended use of the balloon catheter.
- the outer diameter of the straight tube part when expanded is 1.OOmm force 35.OOmm, preferably 1.25mm to 30.OOmm. ⁇ Length force 5.
- Balloon force test for dilatation of stenosis of coronary artery of heart In this case, the outer diameter of the straight pipe section when expanded is 1.25 mm force and 5. Omm.
- the preferred length of the straight pipe section is 7. OOmm to 40.00 mm. preferable.
- the resinous species of the tubular parison is not particularly limited.
- polyolefin, polyolefin elastomer, polyester, polyester elastomer, polyamide, polyamide elastomer, polyurethane and polyurethane elastomer can be used.
- resins such as polycarbonate, polyamide, polyurethane, polysanophone, polyarylate, styrene butadiene copolymer, and polyolefin are preferable. Can be used for
- a core wire may be provided in the catheter for the purpose of prevention.
- the core wire may be disposed in any part of the catheter, but is preferably disposed in a lumen other than the guide wire lumen in order to maintain operability when the catheter is inserted along the guide wire.
- a taper shape in which a part of the outer diameter of the core wire decreases toward the distal end may be used. If the core wire is a metal, the material type is not particularly limited.
- the core wire processing method is not particularly limited, and a method such as centerless polishing is preferably used.
- An X-ray impermeable marker may be provided in order to improve the visibility of a specific part of the catheter during treatment using the catheter according to the present invention and to easily position the catheter.
- the radiopaque marker is a material having radiopaque properties, any kind of material such as resin or resin may be used.
- the position, number, etc. are not limited and can be set according to the purpose of use of the catheter.
- two X-ray opaque markers 11 may be provided on the outer surface of the inner shaft 8 penetrating the balloon 5.
- one X-ray opaque marker 11 may be provided on the outer surface of the inner shaft 8.
- a hydrophilic coating can be applied to the outer surface of the catheter in order to facilitate insertion into a blood vessel or a guide catheter. That is, it is possible to apply a hydrophilic coating that exhibits lubricity when it comes into contact with blood on at least a part of the portion that comes into contact with blood, such as the distal shaft and the proximal shaft.
- the site where the hydrophilic coating is applied and the length of the coating can be determined according to the purpose of use of the catheter.
- hydrophilic polymers such as poly (2-hydroxyethyl methacrylate), polyacrylamide, polybutylpyrrolidone and the like can be suitably used, and the coating method is not limited.
- hydrophobic coating can be applied to the outer surface of the balloon so that the balloon does not slip when the balloon is expanded.
- the kind of the hydrophobic coating is not particularly limited, and a hydrophobic polymer such as polydimethylsiloxane can be suitably used.
- a tubular parison (inner diameter 0.43 mm, outer diameter 0.89 mm) was prepared by extrusion molding using a polyamide elastomer (PEBAX7033SA01, elf atochem), and then biaxial stretch blow molding was performed using this parison.
- the straight pipe has an outer diameter of 3. Omm, the straight pipe has a length of 20 mm, the distal and proximal tapers have a length of 5 mm, and the distal and proximal joints have a length of A 5 mm lane was prepared.
- a tube (inner diameter 0.43 mm, outer diameter 0.56 mm) was produced by extrusion molding using high-density polyethylene (HY540, Nippon Polychem Co., Ltd.). The high-density polyethylene tube was cut into 46 mm and 254 mm. One end of the tube cut to 46 mm was expanded to an inner diameter of 0.58 mm, and one end of the tube cut to 254 mm was inserted into the expanded portion and heat-welded and then used as the inner shaft. The heat welded portion was used as a protrusion.
- a tube (inner diameter 0.72 mm, outer diameter 0.86 mm) was produced by extrusion molding using a polyamide elastomer (PEBAX7233SA01, elf atochem).
- the tube is heat-processed and corresponds to the shape shown in Fig. 11
- An outer shaft was prepared by producing a reduced diameter portion.
- the proximal joint portion of the balloon was thermally welded to the cut end.
- the inner shaft was inserted from the end of the lane and positioned as shown in Fig. 8. At this time, the distance between the proximal end of the protrusion and the distal end of the reduced diameter portion was 1. Omm, and the inner shaft protruded 2 mm further to the distal side than the balloon distal joint.
- the balloon's distal end joint and inner shaft were bonded using a two-component mixed urethane adhesive (-PPPOLAN 4235, Coronate 4403, Nippon Polyurethane Industry Co., Ltd.).
- the outer shaft was cut at 360 mm from the heat welded portion between the balloon and the proximal joint of the outer shaft, and a cut about half a circumference was made in the outer shaft located 260 mm from the heat welded portion.
- the inner shaft and the outer shaft are bonded using the adhesive with the inner shaft exposed from the notch to the outer surface of the outer shaft by about 1 mm, and the proximal end opening end of the guide wire lumen is made distal.
- a side shaft was used.
- the proximal shaft (inner diameter 0.50 mm, outer diameter 0.666 mm, length 1,200 mm) was made of SUS316L alloy.
- the proximal end force of the distal shaft was also inserted at one end of the proximal shaft, and the end of the inserted proximal shaft was adjacent to the proximal open end of the guidewire lumen. In this state, the proximal shaft and the distal shaft were bonded with the adhesive.
- a hub was produced from polycarbonate (Makloron 2658, Bayer) by injection molding.
- a strain relief was produced from a polyamide elastomer (PEBAX5533SA01, elf atochem) by injection molding.
- An example of the balloon catheter according to the present invention was formed by joining the produced strain relief and hub to the proximal end of the proximal shaft.
- the tube with the cross-sectional shape shown in Fig. 15 (diameter of inflation lumen 2a: 0.86mm, thickness: 0.14) mm, the diameter of each inflation lumen 2b: 0.06 mm). Cut the prepared tube to 5mm, and heat weld the tube (inner diameter 0.72mm, outer diameter 0.86mm) made by extrusion using polyamide elastomer (PEBAX723 3SA01, elf atochem) at both ends. This was produced in the same manner as in Example 1 except that the diameter-reduced portion was used.
- PEBAX7233SA01, elf atochem polyamide elastomer
- Example 1 except that the core material 26B (diameter of the large cylindrical portion 27c: 0.4 lmm, the diameter of the small cylindrical portion 27d: 0.16mm) having the shape shown in FIG. 22 was used when producing the reduced diameter portion. It produced similarly.
- Tubes (inner diameter 0.43 mm, outer diameter 0.56 mm) were prepared by extrusion molding using high-density polyethylene (HY540, Nippon Polychem Co., Ltd.). The high density polyethylene tube was cut to 298 mm. An X-ray opaque marker (outer diameter 0.62 mm, inner diameter 0.58 mm, length 1.5 mm) made of platinum-tungsten alloy (tungsten content 8 wt%) is placed at 44 mm from one end of the tube with the adhesive. Glued.
- a tube having a cross-sectional shape shown in Fig. 14 (diameter of inflation lumen 2a: 0.86mm, thickness: 0.14mm, diameter of each inflation lumen 2b: 0.06) was produced by extrusion. Cut the prepared tube to 5mm, and heat weld the tube (inner diameter 0.72mm, outer diameter 0.86mm) made by extrusion using polyamide elastomer (PEBAX723 3SA01, elf atochem) at both ends. In the same manner as in Example 2, except that the diameter-reduced portion was used.
- PEBAX7233SA01, elf atochem polyamide elastomer
- Example 2 Made in the same way as in Example 1 except that a tube (inner diameter 0.72mm, outer diameter 0.86mm, length 40mm) made using a polyamide elastomer (PEBAX6333SA01, elf atochem) was used instead of the balloon.
- a tube inner diameter 0.72mm, outer diameter 0.86mm, length 40mm
- PEBAX6333SA01, elf atochem polyamide elastomer
- a tube (inner diameter 0.72 mm, outer diameter 0.86 mm, length 40 mm) made with a polyamide elastomer (PEBAX6333SA01, elf atochem) is used with an excimer laser.
- An infusion catheter according to the present invention was prepared in the same manner as in Example 1 except that 5 m holes were used instead of the balloon. The holes were 5 mm apart in the axial direction and had one hole on the same circumference, and were arranged so as to form a clockwise spiral by urging toward the distal side of the catheter. The phase difference between adjacent holes was 90 °.
- a comparative example 1 was prepared in the same manner as in Example 1 except that the protrusion and the reduced diameter part were not provided.
- a comparative example 2 was prepared in the same manner as in Example 5 except that the protrusion and the reduced diameter part were not provided.
- a comparative example 3 was prepared in the same manner as in Example 6 except that the protrusion and the reduced diameter portion were not provided.
- a catheter 25 is placed in a polyethylene simulated blood vessel 19 having an inner diameter of 3 mm and an outer diameter of 5 mm fixed to the slide table 20, and the catheter holding portion 22 and the catheter 25 are force gauges. Connected 23.
- the distal end of the catheter 25 was positioned 2 mm from the stainless steel simulated constriction 18.
- a guide wire 21 of 0. 014 inches is inserted in advance into the guide wire lumen of the catheter 25, and the guide wire 21 located on the distal side of the distal end of the catheter 25 has a diameter of 0 provided in the simulated constriction 18 Placed in 45mm hole 24.
- the position of the guide wire distal end was 50 mm distal to the catheter distal end.
- the force gauge 23 holding the catheter 25 is moved in the direction of the stainless steel simulated constriction 18 fixed to the slide table 20.
- the catheter 25 and the force tail holding part 22 move in the direction of the simulated stenosis part 18.
- the force gauge 23 was moved in the direction of the constricted part 18 at a speed of 0.5 mmZsec until a load of 2.5 N was generated.
- the inner shaft and the outer shaft showed good pressability without being nested with each other.
- the resistance obtained when moving the catheter obtained in Examples 1 to 4 through the hole 24 which is a stenosis portion in the evaluation system shown in FIG. It was. Further, the tips of the catheters obtained in Examples 1 to 4 were flexible, and the balloon expansion / contraction response was also good.
- Comparative Example 1 when the load of 1.3N was generated, the balloon was deformed into an accordion shape, and the force could not be transmitted beyond that. In Comparative Examples 2 and 3, which do not have a balloon, 1. When a load of 8 N occurs, the inner shaft and the outer shaft are deformed in a nested manner and cannot transmit any more load. I helped. Industrial applicability
- the catheter of the present invention is a catheter used for medical purposes, more specifically, percutaneous angioplasty (PTA: Percutaneous Transluminal Angioplasty, PTA) when performing peripheral angioplasty, coronary artery formation, valvuloplasty, and the like.
- PTA Percutaneous Transluminal Angioplasty
- PTCA Percutaneous Transluminal Coronary Angioplasty
- PTCA is suitable for use as an infusion catheter that can administer a therapeutic substance to a local site.
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- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- General Health & Medical Sciences (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Pulmonology (AREA)
- Biophysics (AREA)
- Animal Behavior & Ethology (AREA)
- Engineering & Computer Science (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Child & Adolescent Psychology (AREA)
- Physics & Mathematics (AREA)
- Geometry (AREA)
- Media Introduction/Drainage Providing Device (AREA)
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/910,714 US20090270801A1 (en) | 2005-04-06 | 2006-04-05 | Catheter |
EP06731176.1A EP1880742B1 (en) | 2005-04-06 | 2006-04-05 | Catheter |
JP2007512937A JP4985398B2 (ja) | 2005-04-06 | 2006-04-05 | カテーテル |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2005109585 | 2005-04-06 | ||
JP2005-109585 | 2005-04-06 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2006109649A1 true WO2006109649A1 (ja) | 2006-10-19 |
Family
ID=37086926
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2006/307228 WO2006109649A1 (ja) | 2005-04-06 | 2006-04-05 | カテーテル |
Country Status (4)
Country | Link |
---|---|
US (1) | US20090270801A1 (ja) |
EP (1) | EP1880742B1 (ja) |
JP (1) | JP4985398B2 (ja) |
WO (1) | WO2006109649A1 (ja) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2008264118A (ja) * | 2007-04-18 | 2008-11-06 | Kaneka Corp | カテーテル |
JP2008264120A (ja) * | 2007-04-18 | 2008-11-06 | Kaneka Corp | 押圧性を備えたカテーテル |
JP2012183127A (ja) * | 2011-03-04 | 2012-09-27 | Asahi Intecc Co Ltd | バルーンカテーテル |
JP2013022166A (ja) * | 2011-07-19 | 2013-02-04 | Asahi Intecc Co Ltd | バルーンカテーテル |
JP2015013207A (ja) * | 2014-09-22 | 2015-01-22 | 朝日インテック株式会社 | バルーンカテーテル |
JP2015029562A (ja) * | 2013-07-31 | 2015-02-16 | フクダ電子株式会社 | バルーンカテーテル及びバルーンカテーテルに用いられるバルーンの製造方法 |
CN115266388A (zh) * | 2022-09-28 | 2022-11-01 | 江苏科标医学检测有限公司 | 一种血管***测试仪及其工作方法 |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
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DE102007036685A1 (de) * | 2007-08-03 | 2009-02-05 | Innora Gmbh | Verbesserte arzneimittelbeschichtete Medizinprodukte deren Herstellung und Verwendung |
JP5470406B2 (ja) * | 2009-12-28 | 2014-04-16 | テルモ株式会社 | バルーンカテーテル |
US20120046599A1 (en) * | 2010-02-18 | 2012-02-23 | Cardiovascular Systems, Inc. | Therapeutic agent delivery system, device and method for localized application of therapeutic substances to a biological conduit |
US10022127B2 (en) * | 2011-11-02 | 2018-07-17 | Abbott Cardiovascular Systems Inc. | Double bellow occluder for sclerotherapy |
CN110227206B (zh) * | 2012-07-24 | 2022-04-22 | 明讯科技有限公司 | 球囊导管 |
US9427378B2 (en) * | 2013-04-30 | 2016-08-30 | Avent, Inc. | Gastric jejunal tube with an enlarged jejunal lumen |
US20160045719A1 (en) * | 2014-08-15 | 2016-02-18 | Acclarent, Inc. | Shaft system for balloon dilation |
JP6804370B2 (ja) * | 2017-03-31 | 2020-12-23 | テルモ株式会社 | 医療用長尺体 |
US20190054270A1 (en) * | 2017-08-15 | 2019-02-21 | Becton, Dickinson And Company | Anti-occlusion catheter |
US11911054B2 (en) * | 2022-03-22 | 2024-02-27 | Rutgers, The State University Of New Jersey | Neuroaspiration catheter for thrombectomy |
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JP2001276228A (ja) * | 2000-01-24 | 2001-10-09 | Toray Ind Inc | バルーン付カテーテル |
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2006
- 2006-04-05 WO PCT/JP2006/307228 patent/WO2006109649A1/ja active Application Filing
- 2006-04-05 JP JP2007512937A patent/JP4985398B2/ja active Active
- 2006-04-05 US US11/910,714 patent/US20090270801A1/en not_active Abandoned
- 2006-04-05 EP EP06731176.1A patent/EP1880742B1/en not_active Not-in-force
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JPH10179749A (ja) * | 1996-12-24 | 1998-07-07 | Buaayu:Kk | インフュージョンカテーテル |
JP2001520085A (ja) * | 1997-10-17 | 2001-10-30 | マイクロ・セラピューティクス・インコーポレーテッド | 液体塞栓組成物と凝固剤との注入のためのカテーテルシステムおよび方法 |
JP2001276228A (ja) * | 2000-01-24 | 2001-10-09 | Toray Ind Inc | バルーン付カテーテル |
JP2004147737A (ja) * | 2002-10-29 | 2004-05-27 | Nippon Zeon Co Ltd | バルーンカテーテル及びその製造方法 |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
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JP2008264118A (ja) * | 2007-04-18 | 2008-11-06 | Kaneka Corp | カテーテル |
JP2008264120A (ja) * | 2007-04-18 | 2008-11-06 | Kaneka Corp | 押圧性を備えたカテーテル |
JP2012183127A (ja) * | 2011-03-04 | 2012-09-27 | Asahi Intecc Co Ltd | バルーンカテーテル |
US8864705B2 (en) | 2011-03-04 | 2014-10-21 | Asahi Intecc Co., Ltd. | Balloon catheter |
JP2013022166A (ja) * | 2011-07-19 | 2013-02-04 | Asahi Intecc Co Ltd | バルーンカテーテル |
JP2015029562A (ja) * | 2013-07-31 | 2015-02-16 | フクダ電子株式会社 | バルーンカテーテル及びバルーンカテーテルに用いられるバルーンの製造方法 |
JP2015013207A (ja) * | 2014-09-22 | 2015-01-22 | 朝日インテック株式会社 | バルーンカテーテル |
CN115266388A (zh) * | 2022-09-28 | 2022-11-01 | 江苏科标医学检测有限公司 | 一种血管***测试仪及其工作方法 |
Also Published As
Publication number | Publication date |
---|---|
EP1880742A4 (en) | 2010-07-07 |
EP1880742A1 (en) | 2008-01-23 |
US20090270801A1 (en) | 2009-10-29 |
JP4985398B2 (ja) | 2012-07-25 |
EP1880742B1 (en) | 2017-05-31 |
JPWO2006109649A1 (ja) | 2008-11-13 |
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