WO2000043061A1 - Catheter intravasculaire a renfort composite - Google Patents

Catheter intravasculaire a renfort composite Download PDF

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Publication number
WO2000043061A1
WO2000043061A1 PCT/US2000/001412 US0001412W WO0043061A1 WO 2000043061 A1 WO2000043061 A1 WO 2000043061A1 US 0001412 W US0001412 W US 0001412W WO 0043061 A1 WO0043061 A1 WO 0043061A1
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WO
WIPO (PCT)
Prior art keywords
shaft
layer
intravascular catheter
members
axial
Prior art date
Application number
PCT/US2000/001412
Other languages
English (en)
Inventor
Robert J. Garabedian
John Griego
Earl Bardsley
Dean A. Schaefer
Cang D. Dao
Steven M. Anderson
David Paulk
Original Assignee
Boston Scientific Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US09/234,203 external-priority patent/US6171295B1/en
Priority claimed from US09/487,359 external-priority patent/US6942654B1/en
Priority claimed from US09/487,353 external-priority patent/US6709429B1/en
Application filed by Boston Scientific Limited filed Critical Boston Scientific Limited
Priority to EP00906968A priority Critical patent/EP1152788A4/fr
Priority to CA002358661A priority patent/CA2358661A1/fr
Priority to JP2000594514A priority patent/JP4213350B2/ja
Priority to AU28542/00A priority patent/AU2854200A/en
Publication of WO2000043061A1 publication Critical patent/WO2000043061A1/fr

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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
    • A61M25/0043—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

Definitions

  • the present invention generally relates to intravascular catheters. More specifically, the present invention relates to intravascular catheters having reinforcement.
  • Intravascular catheters are used in a wide variety of relatively non-invasive medical procedures. Such intravascular catheters may be used for diagnostic or therapeutic purposes.
  • an intravascular catheter allows a physician to remotely perform a medical procedure by inserting the catheter into the vascular system of the patient at a location that is easily accessible and thereafter navigating the catheter to the desired target site.
  • virtually any target site in the patient's vascular system may be remotely accessed, including the coronary, cerebral, and peripheral vasculature. The distance between the access site and the target site is often in excess of
  • intravascular catheters must be relatively long and thin.
  • intravascular catheters In order to navigate through the patient's tortuous vascular system, intravascular catheters must be very flexible. It is also desirable that intravascular catheters be relatively soft in order to minimize the probability of damaging vascular tissue.
  • Intravascular catheters typically have a radiopaque portion and are guided through the patient's vascular system with the assistance of x-ray fluoroscopy.
  • a physician may manipulate the proximal end of the catheter and fluoroscopically monitor the corresponding movement of the distal end of the catheter.
  • intravascular catheters be sufficiently radiopaque along their length and particularly at their distal end such that the physician is able to clearly monitor the progress of the catheter as it is being advanced from the vascular access site to the vascular target site.
  • the catheter may be used for various diagnostic and/or therapeutic purposes.
  • diagnostic and therapeutic techniques require the infusion of fluids through the catheter.
  • pharmaceutical solutions i.e., drugs
  • intravascular catheters be sufficiently resistant to kinking.
  • intravascular catheters be sufficiently resistant to bursting.
  • prior art intravascular catheters have utilized a reinforcement structure such as a braid or coil disposed between an inner tubular polymer layer and an outer tubular polymer layer.
  • a braid reinforcement structure may offer high resistance to bursting and may improve the integrity of connections between individual shaft segments.
  • a braid reinforcement structure may offer limited resistance to ovaling, which is a precursor to kinking.
  • a coil reinforcement structure may provide adequate resistance to ovaling and kinking, but may not sufficiently enhance the integrity of connections between individual shaft segments.
  • U.S. Patent No. 5,057,092 to Webster discloses an intravascular catheter having a braid reinforcing mesh and longitudinal warp members.
  • the longitudinal warp members are intended to provide increased bending stiffness and thus permit reductions in the wall thickness and/or softer materials for the inner and outer tubes.
  • the warp members are interwoven with the braid such that warp members alternate under or over the braid mesh. Because the braid reinforcing mesh is disposed between an inner polymeric layer and an outer polymeric layer, portions of the longitudinal warp members are disposed between the braid reinforcing mesh and the adjacent polymeric layer.
  • the adjacent polymeric layer may conform to the longitudinal warp members so as to create radial protrusions running the length of the catheter.
  • a protrusion along the inside surface of the catheter may not be desirable because it may create friction or bias with devices inserted therein (e.g., guidewires).
  • a protrusion along the outside surface of the catheter may not be desirable because it may create friction, bias or prevent adequate sealing with devices that the catheter is inserted into (e.g., introducer sheaths, compression fittings, etc.).
  • the adjacent polymeric layer may become fixed to the longitudinal warp members as it conforms thereto. Fixing the longitudinal warp members to the adjacent polymeric layer may not be desirable because it may limit relative movement and flexure therebetween. Limiting relative movement and flexure may cause excessive stiffness in one or more planes of flexure. This may cause difficulties in manipulating and navigating the catheter through tortuous vasculature, which is clearly undesirable.
  • An intravascular catheter in accordance with one embodiment of the present invention includes an elongate shaft having a proximal region, a distal region and a lumen extending therethrough.
  • the proximal region of the shaft includes an inner lubricious polymer layer, a reinforcement layer and an outer layer.
  • the reinforcement layer comprises a braid having at least one metallic member and a plurality of polymer members wherein each polymer member comprises a plurality of monofilaments.
  • the monofilaments may be made of LCP having a substantially circular cross-section and may be fused together or held together statically.
  • the monofilaments may be arranged side-by-side to collectively define a flat cable that may be twisted along the length of the shaft.
  • the metallic member(s) may be made of a highly radiopaque material.
  • the braid reinforcement provides high burst strength and durability.
  • the polymer members of the braid provide enhanced flexibility and softness, and the metallic members(s) of the braid provide enhanced radiopacity and resistance to ovaling and kinking.
  • An intravascular catheter in accordance with another embodiment of the present invention includes an elongate shaft having a proximal region, a distal region and a lumen extending therethrough.
  • the proximal region of the shaft includes an inner lubricious polymer layer, a reinforcement layer and an outer layer.
  • the outer layer includes a proximal portion made of a first material having a first durometer, and a distal portion made of a second material having a second durometer less than the first durometer.
  • the reinforcement layer comprises a braid having one or more metallic members and a plurality of polymer members wherein each polymer member comprises a plurality of monofilaments.
  • the distal region of the shaft includes a radiopaque marker band surrounding the reinforcement layer and an atraumatic tip layer surrounding the radiopaque marker band and the reinforcement layer.
  • the tip layer is made of a third material having a third durometer less than the second durometer.
  • the tip layer includes a distal portion that extends beyond the distal ends of the inner layer and the reinforcement layer to form an atraumatic soft distal tip.
  • An intravascular catheter in accordance with yet another embodiment of the present invention includes a braid reinforcement with one or more axial wires or fibers disposed between the helical members that form the braid.
  • the axial member(s) prevent elongation of the shaft of the catheter thereby maintaining one-to- one correspondence in axial manipulation of the catheter, even when the shaft is placed in tension.
  • the axial member(s) do not create a protrusion on either side of the braid.
  • the axial member(s) do not become fixed to any polymer layer adjacent the braid.
  • this embodiment of the present invention maintains the benefits of axial member(s), but without creating the undesirable effects of friction caused by an axial protrusion and without creating the undesirable effects of limited flexure caused by an adjacent polymer layer becoming fixed to the axial member(s).
  • this embodiment of the present invention provides several other benefits by optionally utilizing a plurality of axial members.
  • Third, the strength of the connections between adjacent shaft segments is increased significantly.
  • the stiffness of the catheter may be uniformly increased thereby potentially reducing the profile of the catheter by allowing the wall thickness and/or hardness of the polymer layers to be reduced.
  • the burst strength of the catheter may be significantly increased by virtue of the axial members limiting radial expansion of the shaft.
  • the axial members are preferably uniformly spaced about the circumference of the shaft. Virtually any number of axial members may be utilized, depending on the particular characteristics desired. For example, four or eight axial members may be utilized wherein the axial members are uniformly spaced apart by 90° or 45°, respectively, about the circumference of the shaft. In addition, only a portion of the shaft may include a plurality of axial members. For example, the distal shaft portion may have fewer axial members than the proximal shaft portion such that the distal shaft portion is more flexible.
  • the axial members may comprise a polymeric material, a metallic material or a combination thereof. If a polymeric material is utilized, then each member may comprise a plurality of monofilaments such as LCP.
  • the monofilaments may be held together statically thereby eliminating the need for a binding material that might otherwise add to the profile of the members.
  • the monofilaments may be arranged side-by-side to collectively define a flat ribbon or cable.
  • the present invention also provides a method of making such a catheter.
  • the manufacturing method includes the steps of braiding two or more helical members about one or more axial members such that the axial members are disposed between the helical members.
  • the axial members are preferably uniformly spaced about the circumference of the shaft.
  • the helical members may be braided over a carrier such as a mandrel that is later removed or a polymeric tubular member that becomes the inner layer of the catheter shaft. After the reinforcement layer is woven about the carrier, another polymeric tubular member may be disposed about the reinforcement layer to become the outer layer of the catheter shaft.
  • Figure 1 is a plan view of an intravascular catheter in accordance with the present invention
  • Figure 2 is a partially sectioned detailed view of the elongate shaft of the catheter illustrated in Figure 1 ;
  • Figure 3 is a cross-sectional view taken along line 3-3 in Figure 1;
  • Figure 4 is an alternative embodiment of the shaft;
  • Figures 5 A and 5B are cross-sectional views of the polymer member of the reinforcement layer;
  • Figure 6 is a cross-sectional view taken along line 3-3 in Figure 1 illustrating another alternative embodiment of the shaft.
  • Figure 7 is a fragmentary partially sectioned side view of the shaft illustrated in Figure 6.
  • FIG. 1 illustrates intravascular catheter 10 in accordance with the present invention.
  • Catheter 10 includes an elongate shaft 12 having a proximal region 14 and a distal region 16.
  • the catheter 10 includes a lumen 18 (as best seen in Figure 3) extending through the entire length of the elongate shaft 12 to an opening at the distal end 20 of the shaft 12.
  • Catheter 10 may have a length of 80 to 150 cm and an outside diameter of approximately 3F.
  • a manifold 24 is connected to the proximal end 22 of the shaft 12 which includes an interior (not visible) in fluid communication with the lumen 18 of the elongate shaft 12.
  • Manifold 24 includes a standard fitting 26 for connection to a fluid source such as a syringe.
  • a strain relief 28 is disposed between the manifold 24 and the proximal end 22 of the shaft 12 in order to reduce the tendency of the shaft to kink therebetween.
  • the proximal end 22 of the elongate shaft 12 may extend through the strain relief 28 for connection to the manifold 24.
  • the distal end of the strain relief 28 may be connected to the proximal end 22 of the elongate shaft 12 with the proximal end of the strain relief 12 connected to the manifold 24.
  • the intravascular catheter 10 provides a fluid path from the fitting 26 of the manifold 24 to the distal end 20 of the elongate shaft 12 by way of the interior (not visible) of the manifold 24 and the lumen 18 of the elongate shaft 12.
  • This intravascular catheter 10 may be advanced over a guide wire and used to deliver diagnostic and/or therapeutic fluids to a desired vascular target site using conventional techniques.
  • Figure 2 is a partially sectioned detailed view of the elongate shaft 12 of the intravascular catheter 10 illustrated in Figure 1. On the top portion of the shaft 12, the outer layer 30 has been removed to expose the reinforcement layer 32 and the axial member 34. On the bottom portion, the shaft 12 has been sectioned to illustrate the various layers 30, 32, 36, and 38 of the shaft 12.
  • Elongate shaft 12 includes a proximal region 14 and a distal region 16. Both the proximal region 14 and a portion of the distal region 16 include an inner lubricious polymer layer 36 surrounded by a reinforcement layer 32 which, in turn, is surrounded by an outer layer 30.
  • the outer layer 30 may be loaded with a radiopaque contrast material such as barium sulfate, preferably loaded at 30% by weight.
  • a tie layer 38 may be provided between the reinforcement layer 32 and the inner lubricious layer 36.
  • Inner layer 36 is formed of a lubricious polymer such as PTFE or HDPE and preferably has a relatively thin wall to minimize profile.
  • Inner layer 26 has an inside diameter sufficiently large to accommodate a conventional guidewire and to accommodate the delivery of fluids therethrough at a sufficient flow rate.
  • the inside diameter of the inner layer 36 may be approximately 0.027 inches and the wall thickness of the inner layer 36 may be approximately 0.0005 inches.
  • the inner layer 36 may be formed, for example, by coating or extruding a lubricious polymer such as PTFE over a removable mandrel, or by using other known manufacturing techniques.
  • a tie layer 38 may be utilized to secure the reinforcement layer 32 to the inner lubricious layer 36.
  • Tie layer 38 enhances the bond between the inner lubricious layer 36, the reinforcement layer 32, and the outer layer 30. Tie layer 38 also fills any micro-pores that may form in the inner layer 36 to thereby increase burst strength. Further, tie layer 38 maintains the position of the reinforcement layer 32 on the inner layer 36 during the manufacturing process. The thickness of the tie layer 38 may be approximately 0.0003 inches to reduce the corresponding increase in profile.
  • An example of a suitable material for tie layer 38 is polyurethane, which may be coated onto the inner lubricious layer 36.
  • Reinforcement layer 32 comprises a braid including a plurality of helical polymer members 40 and one or more helical metallic members 42.
  • the reinforcement layer 32 in the form of a braid having a total of eight members may comprise six polymer members 40 and two metallic members 42.
  • the braid reinforcement layer 32 may vary in pattern, strand quantity, pick-count, etc., without departing from the scope of the present invention.
  • Each polymer member 40 comprises a plurality of monofilaments 41 to collectively define a cable 40A or 40B, illustrated in Figures 5A and 5B, respectively.
  • Figures 5 A and 5B show cross-sectional views of the polymer cables 40A and 40B of the reinforcement layer.
  • Figure 5A illustrates a round cable 40A
  • Figure 5B illustrates a flat cable 40B.
  • the monofilaments 41 may be unfused or fused together depending on the desired characteristics. Unfused monofilaments 41 may be held together statically thereby eliminating the need for a binding material that might otherwise add to the profile of the shaft 12. To further minimize profile, the monofilaments 41 may be arranged side-by-side to collectively define a flat ribbon or cable. If the monofilaments 41 are fused together, the polymer member 40 has mechanical characteristics similar to that of a solid rod. If the monofilaments 41 are not fused together, the polymer member 40 has mechanical characteristics similar to that of a cable. A cable, as opposed to a solid rod, is more flexible and is able to withstand more fatigue due to repeated bending.
  • a reinforcement layer 32 utilizing braided polymer members 40 comprising a plurality of unfused monofilaments 41 provide a shaft 12 that is more flexible and more durable.
  • the monofilaments 41 may be made of a liquid crystal polymer (LCP) available under the trade name VECTRAN. Each monofilament may have a circular cross-section having a diameter of 0.0007 inches.
  • Each polymer member 40 may comprise two (2) to ten (10), and preferably five (5) monofilaments 41 which, as stated previously, may be fused or held together statically (i.e., unfused). If the monofilaments 41 are held together statically, the monofilaments of the polymer member 40 are typically arranged side-by-side to essentially define a flat cable 40B as shown in Figure 5B. It is possible, however, that the monofilaments be arranged in any manner to collectively define a flat cable 40B, a round cable 40 A, or any other desired geometry.
  • the flat cable 40B may be twisted along the length of the catheter shaft 12.
  • the flat cable 40B has a pair of major sides 43 and a pair of minor sides 45. Each of the major sides 43 faces the lumen 18 at various points along the length of the shaft 12.
  • the flat cable may have random twists or a twist every 7.5 inches, depending on manufacturing conditions. Twisting the flat cable 40B may provide the advantage of improved guide wire movement due to ridges formed on the inside surface of the inner layer 36.
  • the metallic member 42 may be formed of stainless steel or a highly radiopaque material such as gold, tungsten, iridium, or an alloy thereof. If a plurality of metallic members 42 are utilized, one or more of the metallic members 42 may comprise stainless steel to provide superior strength and one or more metallic members 42 may comprise a highly radiopaque material to provide enhanced radiopacity. Although stainless steel provides higher radiopacity relative to most polymers, a more dense material such as those identified above are preferred for purposes of radiographic visualization.
  • the metallic members 42 may have a rectangular cross-section or a circular cross-section, depending on the desired mechanical characteristics. Metallic member 42 may have a circular cross-section with a diameter of approximately 0.0016 inches to minimize profile.
  • An axial member 34 is disposed between the reinforcement layer 32 and the tie layer 38 to provide enhanced resistance to elongation as the catheter 10 is removed from the patient's body.
  • the axial member 34 may be an LCP flat cable, similar to cable 40B.
  • the axial member 34 may be replaced by the axial member(s) 64 discussed with reference to Figures 6 and 7.
  • the reinforcement layer 32 provides superior flexibility and softness by virtue of the polymer members 40 in addition to superior radiopacity and kink resistance by virtue of the metallic member(s) 42.
  • the ILC portion 44 of outer layer 30 includes a proximal portion 47 formed of a relatively high durometer polymer and a distal portion 49 formed of a relatively low durometer polymer.
  • the proximal region 14 gradually transitions from the relatively high durometer polymer 47 to the relatively low durometer polymer 49.
  • the transition between the relatively high durometer polymer 47 to the relatively low durometer polymer 49 is graphically illustrated by transition line 46.
  • transition line 46 is typically not visible due to the intermixing of polymers during the ILC process.
  • the ILC portion 44 may be formed of a suitable polymer such as polyether block amide having a wall thickness of approximately 0.0025 inches.
  • the proximal ILC portion 47 may be formed of PEBAXTM 7233, which has a durometer of 72D and the distal ILC portion 49 may be formed of PEBAXTM 3533 having a durometer of 35D.
  • the proximal region 14 of the outer layer 30 abuts the distal region 16 of the outer layer 30 at junction line 48.
  • the distal region 16 of the shaft 12 includes a proximal portion 50 and a distal portion 52. Both the proximal portion 50 and the distal portion 52 of the distal region 16 may be formed of the same or different polymers which have a durometer less than the durometer of the distal portion 49 of the ILC section 44.
  • the distal portion 52 of the distal region 16 may have the same or lower durometer than the durometer of the proximal portion 50.
  • the proximal portion 50 and the distal portion 52 may be formed of a polyether block amide polymer such as PEBAXTM 2533 having a durometer of 25D.
  • the proximal portion 50 encapsulates the radiopaque marker band 60.
  • Radiopaque marker band 60 may be formed of gold, tungsten, iridium, or an alloy thereof.
  • the radiopaque marker band 60 is disposed over the reinforcement layer 32 and may optionally be swaged onto the reinforcement layer 32.
  • the radiopaque marker band 60 may optionally be adhesively secured to the reinforcement layer 32 or held in place by the encapsulating proximal portion 50.
  • the distal portion 52 of the distal region 16 abuts the distal ends of the various layers 36, 38, and 32 and forms a lap joint with proximal portion 50 along junction line 54.
  • Junction line 54 between the proximal portion 50 of the outer layer 30 and the distal portion 52 is not present if the proximal portion 50 and the distal portion 52 are made of the same material, i.e., the proximal portion 50 and the distal portion 52 form a single unitary piece.
  • Encapsulated marker band 60 may have a length of approximately 1.0 mm and may be positioned approximately 0.5 to 1.5 mm proximal of the distal end of the shaft 12.
  • Distal portion 52 may extend approximately 0.5 to 1.0 mm beyond the distal end of the inner layer 36, tie layer 38 and reinforcement layer 32 to form an atraumatic soft tip.
  • Figure 4 is an alternate embodiment of the elongate shaft 12 illustrated in Figure 2. Specifically, Figure 4 illustrates an alternative arrangement of the outer layer 30 of the distal region 16 of the elongate shaft 12. Except as described herein, all aspects of the embodiment illustrated in Figure 4 are the same as those described with reference to the embodiment illustrated in Figure 2.
  • Distal region 16 includes a proximal portion 70 and a distal portion 72.
  • Proximal portion 70 and distal portion 72 may be formed of the same materials as proximal portion 50 and distal portion 52, respectively, as described with reference to Figure 2.
  • Distal portion 72 encapsulates the outer surface and distal face of the marker band 60.
  • Distal portion 72 and proximal portion 70 are connected by a lap joint as defined by junction line 74. Junction line 74 between the proximal portion 70 and the distal portion 72 is not present if the proximal portion 70 and the distal portion 72 are formed of the same or similar materials.
  • Distal portion 72 is approximately 2.5 to 3.0 mm in length and extends approximately 1.0 mm beyond the distal ends of the inner layer 36, the tie layer 38, and the reinforcement layer 32 to form an atraumatic tip.
  • the elongate shaft 12, including the embodiment illustrated in Figure 2 and the embodiment illustrated in Figure 4, may be manufactured by a number of suitable manufacturing processes including the process described hereinafter.
  • the inner layer 36 and the tie layer 38 may be obtained prefabricated from a suitable vendor, such as HN. Technologies, and provided as discrete tubes or on a spool as a continuous tube.
  • Axial member 34 is then disposed on the tube of inner layer 36 and tie layer 38.
  • the axial member 34 may be applied during the braiding step.
  • the reinforcement layer 32 is then braided over the axial member 34 and the tube of inner layer 36 and tie layer 38. The braided subassembly is subsequently cut to the desired length.
  • the marker band 60 is slid over the reinforcement layer 32 into position adjacent the distal end 20 of the elongate shaft 12.
  • the proximal portion 50, 70 of the distal region 16 is slid over the reinforcement layer 32 adjacent the marker band 60.
  • the proximal region 14 comprising a prefabricated ILC tube 44 is slid over the proximal end 22 of the elongate shaft 12.
  • a heat shrink tube e.g., FEP
  • FEP heat shrink tube
  • the heat shrink tube is then removed, exposing the completed shaft 12 subassembly.
  • the manifold 24 and the strain relief 28 are then attached to the proximal end 22 of the elongate shaft 12 using conventional techniques.
  • the catheter 10 is then tested for minimum performance criteria including burst pressure.
  • the distal end 20 of the elongate shaft 12 is then trimmed to the desired length, and the distal portion 52, 72 of the distal region 16 is thermally fused thereto by, for example, inserting a mandrel into the lumen 18 and heating the tip 20 at 350° F for twenty-six (26) seconds.
  • a lubricious coating is then applied to exterior of the catheter shaft 12.
  • the axial member 34 may be replaced with one or more axial members 64 as illustrated in Figures 6 and 7. Except as described hereinafter, the embodiment illustrated in Figures 6 and 7 is the same as the embodiment illustrated in Figure 2.
  • Figure 6 is a cross-sectional view taken along line 3-3 in Figure 1
  • Figure 7 is a fragmentary partially sectioned side view of the shaft 12.
  • the outer layer 30 has been removed to expose the braid reinforcement layer 60 comprising helical members 62 (individually designated as 62A and 62B) and the axial members 64 (individually designated as 64A, 64B, 64C and 64D).
  • the axial members 64 are disposed between the helical members 62 A and 62B and are preferably uniformly spaced about the circumference of the shaft 12.
  • the inner lubricious polymer layer 36 is surrounded by the braid reinforcement layer 60 which, in turn, is surrounded by the outer layer 30.
  • a tie layer 38 may be provided between the braid reinforcement layer 60 and the inner lubricious layer 36.
  • This multi-layer construction may be used in either the proximal region 14 or both the proximal 14 and distal 16 regions, depending on the pushability, trackability, and other characteristics desired for each region.
  • the helical members 62 are interwoven to form a tubular braid.
  • the helical members 62 may comprise a polymeric material, a metallic material or a combination thereof as discussed previously with regard to helical members 40 and 42.
  • Polymeric helical members 62 provide superior flexibility and softness
  • metallic helical members 62 provide superior radiopacity and kink resistance
  • a combination of polymeric and metallic helical members 62 provide a combination of these attributes.
  • One or more axial members 64 may be utilized. Virtually any number of axial members 64 may be utilized, depending on the particular characteristics desired. For example, four or eight axial members 64 may be utilized wherein the axial members 64 are uniformly spaced apart by 90° or 45°, respectively, about the circumference of the shaft 12. In addition, only a portion of the shaft 12 may include a plurality of axial members 64. For example, the distal shaft portion 16 may have fewer axial members 64 than the proximal shaft portion 14 such that the distal shaft portion 16 is more flexible. Axial members 64 may comprise any of the same or similar structures and materials as helical members 62.
  • the axial members 64 may each comprise a set of monofilaments which may be fused together or unfused depending on the desired characteristics. Unfused monofilaments may be held together statically thereby eliminating the need for a binding material that might otherwise add to the profile of the shaft 12. To further minimize profile, the monofilaments may be arranged side-by-side to collectively define a flat ribbon or cable.
  • each axial member 64 comprises a plurality of LCP monofilaments arranged side-by-side as a flat cable, as best seen in Figure 6.
  • the axial members 64 limit elongation of the shaft 12 when the catheter 10 is placed in tension.
  • the catheter 10 may be placed in tension when the catheter 10 is retracted in the proximal direction or withdrawn from a patient's vascular system and some resistance to movement is encountered. If the resistance to movement is encountered distal of the proximal end 22, the catheter shaft 12 is placed in tension.
  • the axial members 64 limit elongation of the shaft. Further, the axial members 64 maintain one-to-one correspondence between axial manipulation of the proximal end 22 and axial movement of the distal end 20 of the shaft 12, even when the catheter 10 is placed in tension. By maintaining one-to-one correspondence in axial manipulation, the axial members 64 maintain precise control of the catheter 10.
  • the axial members 64 do not create a radial protrusion or become fixed to an adjacent polymer layer, both of which may create undesirable effects.
  • radial protrusions may extend along the length of the inner layer 36 or the outer layer 30.
  • protrusions along the inside surface of the catheter 10 may not be desirable because they may create friction or bias with devices inserted into the lumen 18.
  • protrusions along the outside surface of the catheter 10 may not be desirable because they may create friction, bias, or prevent adequate sealing with devices that the catheter 10 is inserted into.
  • Utilizing even a single axial member 64 prevents axial elongation of the shaft 12 and thereby maintains one-to-one correspondence in axial manipulation of the catheter 10.
  • Utilizing a plurality of axial members 64 provides a number of other advantages. By equally spacing the axial members 64 about the circumference of the shaft 12, the shaft 12 maintains uniform flexibility in several planes of flexure corresponding to the number of axial members used. The greater the number of axial members used, the greater number of planes of uniform flexibility. Uniform flexibility provides precise control of the catheter 10 as it is navigated through tortuous vasculature. As compared to a single axial member, uniform spacing of the axial members
  • the 64 about the circumference of the shaft 12 also reduces the likelihood of causing the catheter to curl when the lumen 18 of the catheter 10 becomes clogged and the catheter 10 is pressurized. This may be encountered, for example, if the catheter 10 is utilized to deliver embolic material that unintentionally occludes the lumen 18. By reducing the likelihood of curling, the likelihood of causing trauma to the interior of the vessel wall is also reduced.
  • the axial members 64 also increase the strength of the connections between adjacent shaft segments and the burst strength of the shaft 12.
  • the axial members further provide additional stiffness to the catheter shaft 12 such that the wall thickness and/or hardness of the polymer layers 30 and 36 may be reduced.
  • the catheter 10 may be made as discussed previously with some modifications to the braiding step.
  • braiding helical members is well known in the art, positioning axial members between the helical members requires some modification to conventional braiding machines.
  • a conventional Steeger braiding machine may be modified to incorporate individual bobbin carriers that deliver the axial members 64 through a horn gear shaft.
  • the axial member 64 carriers are retrofitted onto the horn gear.
  • one of the helical member 62A carriers is allowed to pass under and the other helical member 62B carrier is allowed to pass over the axial members 64.
  • the net result is a braid reinforcement structure 60 comprising two or more interwoven helical members 62, with one or more axial members 64 disposed therebetween.

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Abstract

L'invention concerne un cathéter intravasculaire (10) qui possède une combinaison de caractéristiques: de plus grandes souplesse, douceur et radio-opacité et une meilleure résistance à l'ovalisation et au vrillage. La région proximale (14) d'un arbre (12) comprend une couche polymère interne lubrifiante (26), une couche de renfort (32) et une couche externe (30). La couche de renfort (32) peut comprendre une tresse comportant deux ou plusieurs composants métalliques (42) et plusieurs filaments uniques (41), de préférence en LCP. Les éléments polymères de la tresse assurent une meilleure souplesse et une plus grande douceur, en plus d'une pression d'éclatement plus élevée. Les éléments métalliques de la tresse assurent une plus grande radio-opacité et une meilleure résistance à l'ovalisation et au vrillage. Le cathéter (10) peut aussi comprendre un ou plusieurs éléments axiaux disposés entre les éléments hélicoïdaux formant la tresse. Les éléments axiaux (34) offrent un certain nombre d'avantages, y compris le maintien de la correspondance un pour un lors des manipulations axiales, le maintien d'une flexibilité uniforme dans plusieurs plans de flexion, la réduction des risques d'un effet d'enroulement, l'augmentation uniforme de la rigidité du cathéter et l'augmentation de la pression d'éclatement.
PCT/US2000/001412 1999-01-20 2000-01-20 Catheter intravasculaire a renfort composite WO2000043061A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP00906968A EP1152788A4 (fr) 1999-01-20 2000-01-20 Catheter intravasculaire a renfort composite
CA002358661A CA2358661A1 (fr) 1999-01-20 2000-01-20 Catheter intravasculaire a renfort composite
JP2000594514A JP4213350B2 (ja) 1999-01-20 2000-01-20 複合補強材を備えた脈管カテーテル
AU28542/00A AU2854200A (en) 1999-01-20 2000-01-20 Intravascular catheter with composite reinforcement

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US09/234,203 US6171295B1 (en) 1999-01-20 1999-01-20 Intravascular catheter with composite reinforcement
US09/234,203 1999-01-20
US09/487,359 2000-01-19
US09/487,359 US6942654B1 (en) 2000-01-19 2000-01-19 Intravascular catheter with axial member
US09/487,353 2000-01-19
US09/487,353 US6709429B1 (en) 2000-01-19 2000-01-19 Intravascular catheter with multiple axial fibers

Publications (1)

Publication Number Publication Date
WO2000043061A1 true WO2000043061A1 (fr) 2000-07-27

Family

ID=27398531

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/001412 WO2000043061A1 (fr) 1999-01-20 2000-01-20 Catheter intravasculaire a renfort composite

Country Status (5)

Country Link
EP (1) EP1152788A4 (fr)
JP (1) JP4213350B2 (fr)
AU (1) AU2854200A (fr)
CA (1) CA2358661A1 (fr)
WO (1) WO2000043061A1 (fr)

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WO2003004083A1 (fr) * 2001-07-03 2003-01-16 Boston Scientific Limited Catheter pourvu d'un tressage opaque aux rayons x compose de fils de differents diametres
WO2003013640A1 (fr) * 2001-08-06 2003-02-20 Boston Scientific Limited Polymere integre et renfort tresse pour catheters intravasculaires
FR2851472A1 (fr) * 2003-02-26 2004-08-27 Medtronic Vascular Inc Catheter possedant un segment integre hautement radio-opaque et procede de fabrication de ce catheter
WO2005061037A1 (fr) * 2003-12-17 2005-07-07 Boston Scientific Limited Tresse de catheter composite
US7128862B2 (en) 2001-07-03 2006-10-31 Scimed Life Systems, Inc. Biaxially oriented multilayer polymer tube for medical devices
US7824392B2 (en) 2003-08-20 2010-11-02 Boston Scientific Scimed, Inc. Catheter with thin-walled braid
DE102010041112A1 (de) 2010-09-21 2012-03-22 Robert Bosch Gmbh Durchflussmessgerät für einen Flüssigkeitsbehälter und Verfahren zur Hydrationsüberwachung eines Patienten
WO2013163366A1 (fr) * 2012-04-26 2013-10-31 Cook Medical Technologies Llc Gaine renforcée longitudinalement
CN103566449A (zh) * 2012-08-07 2014-02-12 朝日英达科株式会社 导管
US9011745B2 (en) 2010-06-10 2015-04-21 Kaneka Corporation Method for manufacturing a medical tube
US9999749B2 (en) 2013-01-30 2018-06-19 Asahi Intecc Co., Ltd. Catheter
WO2022166538A1 (fr) * 2021-02-05 2022-08-11 微创神通医疗科技（上海）有限公司 Couche de renforcement de cathéter et cathéter
CN115227940A (zh) * 2022-06-30 2022-10-25 河南驼人贝斯特医疗器械有限公司 一种新型复合导管编织层及其混合编织方法
EP4272798A4 (fr) * 2021-02-05 2024-07-03 Microport Neurotech Shanghai Co Ltd Couche de renforcement de cathéter et cathéter

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JP2006181258A (ja) * 2004-12-28 2006-07-13 Kaneka Corp マイクロカテーテルの製造方法及びマイクロカテーテル
US20080317991A1 (en) * 2007-06-19 2008-12-25 Tyco Electronics Corporation Multiple wall dimensionally recoverable tubing for forming reinforced medical devices
JPWO2010067875A1 (ja) 2008-12-11 2012-05-24 株式会社カネカ 医療用チューブ
JP5814530B2 (ja) * 2010-09-08 2015-11-17 株式会社カネカ 医療用カテーテル
JP5873349B2 (ja) * 2012-02-09 2016-03-01 テルモ株式会社 カテーテル
US20140083969A1 (en) * 2012-09-27 2014-03-27 Stryker Nv Operations Limited Method of manufacturing a variably reinforced elongate medical device
JP5885302B2 (ja) * 2012-10-29 2016-03-15 日本ライフライン株式会社 医療機器
CN108135591B (zh) * 2016-02-24 2021-05-28 禾木（中国）生物工程有限公司 柔性增强的神经血管导管
CN110381855B (zh) 2017-01-06 2023-07-04 因赛普特有限责任公司 用于动脉瘤治疗装置的抗血栓涂层
US11395665B2 (en) 2018-05-01 2022-07-26 Incept, Llc Devices and methods for removing obstructive material, from an intravascular site
EP3787523A4 (fr) 2018-05-01 2022-02-23 Incept, LLC Dispositifs et procédés de retrait de matériau obstructif d'un site intravasculaire
US11471582B2 (en) 2018-07-06 2022-10-18 Incept, Llc Vacuum transfer tool for extendable catheter
US11517335B2 (en) 2018-07-06 2022-12-06 Incept, Llc Sealed neurovascular extendable catheter
US11766539B2 (en) 2019-03-29 2023-09-26 Incept, Llc Enhanced flexibility neurovascular catheter
JP2022551988A (ja) 2019-10-15 2022-12-14 インパラティブ、ケア、インク． 多変量的に脳卒中を検出するためのシステム及び方法
US20210316127A1 (en) 2019-12-18 2021-10-14 Imperative Care, Inc. Hemostasis valve
CA3162704A1 (fr) 2019-12-18 2021-06-24 Imperative Care, Inc. Methodes et systemes pour le traitement d'une maladie thromboembolique veneuse
US11553935B2 (en) 2019-12-18 2023-01-17 Imperative Care, Inc. Sterile field clot capture module for use in thrombectomy system
JP2023517575A (ja) 2020-03-10 2023-04-26 インパラティブ、ケア、インク． 可撓性を増強した神経血管カテーテル
US11207497B1 (en) 2020-08-11 2021-12-28 Imperative Care, Inc. Catheter with enhanced tensile strength

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Cited By (21)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7128862B2 (en) 2001-07-03 2006-10-31 Scimed Life Systems, Inc. Biaxially oriented multilayer polymer tube for medical devices
WO2003004083A1 (fr) * 2001-07-03 2003-01-16 Boston Scientific Limited Catheter pourvu d'un tressage opaque aux rayons x compose de fils de differents diametres
WO2003013640A1 (fr) * 2001-08-06 2003-02-20 Boston Scientific Limited Polymere integre et renfort tresse pour catheters intravasculaires
FR2851472A1 (fr) * 2003-02-26 2004-08-27 Medtronic Vascular Inc Catheter possedant un segment integre hautement radio-opaque et procede de fabrication de ce catheter
US7399296B2 (en) 2003-02-26 2008-07-15 Medtronic Vascular, Inc. Catheter having highly radiopaque embedded segment
US7824392B2 (en) 2003-08-20 2010-11-02 Boston Scientific Scimed, Inc. Catheter with thin-walled braid
US8251976B2 (en) 2003-08-20 2012-08-28 Boston Scientific Scimed, Inc. Medical device incorporating a polymer blend
WO2005061037A1 (fr) * 2003-12-17 2005-07-07 Boston Scientific Limited Tresse de catheter composite
US7955313B2 (en) 2003-12-17 2011-06-07 Boston Scientific Scimed, Inc. Composite catheter braid
US9011745B2 (en) 2010-06-10 2015-04-21 Kaneka Corporation Method for manufacturing a medical tube
DE102010041112A1 (de) 2010-09-21 2012-03-22 Robert Bosch Gmbh Durchflussmessgerät für einen Flüssigkeitsbehälter und Verfahren zur Hydrationsüberwachung eines Patienten
WO2013163366A1 (fr) * 2012-04-26 2013-10-31 Cook Medical Technologies Llc Gaine renforcée longitudinalement
US9622892B2 (en) 2012-04-26 2017-04-18 Cook Medical Technologies Llc Longitudinally reinforced sheath
EP2695635A1 (fr) * 2012-08-07 2014-02-12 Asahi Intecc Co., Ltd. Cathéter
US8986284B2 (en) 2012-08-07 2015-03-24 Asahi Intecc Co., Ltd. Catheter
CN103566449A (zh) * 2012-08-07 2014-02-12 朝日英达科株式会社 导管
US9999749B2 (en) 2013-01-30 2018-06-19 Asahi Intecc Co., Ltd. Catheter
WO2022166538A1 (fr) * 2021-02-05 2022-08-11 微创神通医疗科技（上海）有限公司 Couche de renforcement de cathéter et cathéter
EP4272798A4 (fr) * 2021-02-05 2024-07-03 Microport Neurotech Shanghai Co Ltd Couche de renforcement de cathéter et cathéter
CN115227940A (zh) * 2022-06-30 2022-10-25 河南驼人贝斯特医疗器械有限公司 一种新型复合导管编织层及其混合编织方法
CN115227940B (zh) * 2022-06-30 2023-11-14 河南驼人贝斯特医疗器械有限公司 一种复合导管编织层的混合编织方法

Also Published As

Publication number Publication date
CA2358661A1 (fr) 2000-07-27
EP1152788A1 (fr) 2001-11-14
AU2854200A (en) 2000-08-07
EP1152788A4 (fr) 2007-06-27
JP2002535049A (ja) 2002-10-22
JP4213350B2 (ja) 2009-01-21

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