US20040089969A1 - Reinforced catheter and method of manufacture - Google Patents
Reinforced catheter and method of manufacture Download PDFInfo
- Publication number
- US20040089969A1 US20040089969A1 US10/701,699 US70169903A US2004089969A1 US 20040089969 A1 US20040089969 A1 US 20040089969A1 US 70169903 A US70169903 A US 70169903A US 2004089969 A1 US2004089969 A1 US 2004089969A1
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- polymer
- reinforcing member
- mandrel
- catheter
- inner tubular
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
- A61M25/0012—Making of catheters or other medical or surgical tubes with embedded structures, e.g. coils, braids, meshes, strands or radiopaque coils
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
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- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
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- General Health & Medical Sciences (AREA)
- Public Health (AREA)
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- Media Introduction/Drainage Providing Device (AREA)
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Abstract
A catheter shaft is disclosed that may reduce the thickness of the inner layer and/or may allow the reinforcing layer to share the same space as the inner lubricious layer. In one illustrative embodiment, the inner lubricious layer is removed altogether, and an inner tubular braid member defines the inner lumen of the catheter shaft. In another illustrative embodiment, the inner lubricious layer and the reinforcing layer are effectively combined to form a reinforcing member. To combine the inner lubricious layer and the reinforcing layer, the wires used to form the reinforcing braid or coil are first coated with a lubricious polymer such as PTFE or PFA. When these strands are wound to form the tubular reinforcing member, the inner surface of the reinforcing member includes a lubricious surface. Various methods are also disclosed for providing a smooth inner surface for the catheter shaft.
Description
- The present invention generally relates to the field of intravascular medical devices, and more specifically to the field of catheters such as guide catheters used for the placement of medical devices and diagnostic catheters used to inject radiopaque fluids within the body for treatment and diagnosis of vascular diseases. In particular, the present invention relates to an improved reinforced guide or diagnostic catheter and methods of manufacture.
- Several types of catheters are utilized for intravascular treatment. Examples of intravascular catheters include guide catheters, angioplasty catheters, stent delivery devices, angiography catheters, neuro catheters, and the like.
- Guide catheters are commonly used during coronary angioplasty procedures to aid in delivering a balloon catheter or other interventional medical devices to a treatment site in a coronary vessel. In a coronary angioplasty procedure, a guide catheter is introduced into a peripheral artery and advanced over a guidewire through the aorta until the distal end of the guide catheter is engaged with the appropriate coronary ostium. Next, a balloon dilatation catheter is introduced over a guidewire and through the guide catheter. The guidewire is advanced past the distal end of the guide catheter within the lumen of the diseased vessel and manipulated across the region of the stenosis. The balloon dilatation catheter is then advanced past the distal end of the guide catheter, over the guidewire, until the balloon is positioned across the stenotic lesion. After the balloon is inflated to dilate the blood vessel in the region of the stenotic lesion, the guidewire, balloon dilatation catheter and guide catheter are withdrawn.
- Guide catheters typically have preformed bends formed along their distal portion to facilitate placement of the distal end of the guide catheter into the ostium of a particular coronary artery of a patient. In order to function efficiently, guide catheters generally require a relatively stiff main body portion and soft distal tip. The stiff main body portion gives the guide catheter sufficient “pushability” and “torqueability” to allow the guide catheter to be inserted, moved and rotated in the vasculature to position the distal end of the catheter at the desired site adjacent to a particular coronary artery. However, the distal portion should have sufficient flexibility so that it can track over a guidewire and be maneuvered through a tortuous path to the treatment site. In addition, a soft distal tip at the very distal end of the catheter should be used to minimize the risk of causing trauma to a blood vessel while the guide catheter is being moved through the vasculature to the proper position.
- Angiography catheters can be used in evaluating the progress of coronary artery disease in patients. Angiography procedures are used to view the patency of selected blood vessels. In carrying out this procedure, a diagnostic catheter having a desired distal end curvature configuration may be advanced over a guidewire through the vascular system of the patient until the distal end of the catheter is steered into the particular coronary artery to be examined.
- For most intravascular catheters, it is desirable to have both a small outer diameter and a large inner lumen. Having a small outer diameter allows the catheter to be maneuvered more easily once inserted into the body, and may allow the catheter to reach more distal sites. Having a large inner lumen allows larger medical appliances to be inserted through the catheter and/or allows a higher volume of fluids to be injected through the inner lumen. To minimize the outer diameter of the catheter and maximize the inner diameter of the inner lumen, a relatively thin catheter wall is needed.
- Thin-walled catheters formed strictly from polymers such as polyether block amide often do not have sufficient strength to be useful in many medical procedures. The pushability, torqueability, kinkability and other characteristics are often not acceptable. One way to increase the strength of such a thin-walled catheter is to provide a reinforcing braid or coil in the catheter wall. One such catheter is shown in U.S. Pat. No. 4,516,972 to Samson. Samson discloses an intravascular catheter that has an inner lubricious layer (e.g., PTFE), an intermediate reinforcing layer (braid), and an outer layer. The inner lubricious layer reduces the friction of the wall of the inner lumen, which is particularly useful when dilatation catheters or other medical devices are passed through the inner lumen. The braided reinforcing layer is braided over the lubricious layer, and the outer layer is extruded over the reinforcing layer.
- While Samson improves the strength of the catheter wall, the ability to minimize the thickness of the catheter wall is limited. For example, the minimum thickness of the inner lubricous layer of Samson typically must be sufficiently thick to ensure that the lubricious layer remains structurally intact during subsequent processing steps, such as when the reinforcing layer is braided thereover. In addition, the braided reinforcing layer does not penetrate the outer surface of the inner lubricious layer. Instead, the braided reinforcing layer overlays the outer surface of the lubricious layer. As such, the braided reinforcing layer does not share the same space as the inner lubricious layer, thereby adding to the overall thickness of the catheter wall. Finally, because three separate layers must be assembled to form the catheter, the manufacturing costs may be relatively high.
- The present invention provides a reinforced catheter shaft that may have a reduced wall thickness and/or lower manufacturing cost than the prior art. This is preferably achieved by eliminating or reducing the thickness of the inner lubricious layer and/or allowing the reinforcing layer to share the same space as the inner lubricious layer. In one illustrative embodiment, the inner lubricious layer is removed altogether, and an inner tubular formed braid member defines the inner lumen of the catheter shaft. In another illustrative embodiment, the inner lubricious layer and the reinforcing layer are effectively combined to form a reinforcing member. This is accomplished by, for example, coating the wires used to form the reinforcing member with a lubricious polymer such as polytetrafluoroethylene (PTFE) or perfluoroalkoxy (PFA) to first form coated wire. When these coated wires are wound or braided on a mandrel to form the tubular reinforcing member, the inner surface of the reinforcing member includes the lubricious polymer exposed to the inner lumen and forming the lumen wall.
- To provide a smooth inner surface on the lumen wall, the braided or wound reinforcing member may first be disposed on a mandrel that has a relatively smooth outer surface. Heat and/or pressure may then be used to cause the lubricious polymer that coats the core wires of the reinforcing member to conform to the outer surface of the mandrel.
- If a non-thermoplastic polymer such as PTFE is used to coat the core wires, significant heat and pressure may be required to induce the non-thermoplastic polymer to conform to the outer surface of the mandrel. In such a case, the mandrel may be metallic, and more specifically, may be copper or copper coated with silver. If a thermoplastic polymer such as a perfluoroalkoxy polymer (PFA or MFA) is used to coat the core wires of the reinforcing member, less heat may be required to induce the thermoplastic polymer to flow and conform to the smooth outer surface of the mandrel. Accordingly, the mandrel may be made from a polymer, such as acetyl polymer. In this latter case, the cost of the mandrel may be significantly reduced relative to a copper or silver coated copper mandrel. In either case, an outer layer is preferably extruded over the reinforcing member to provide additional support to the catheter shaft and to provide a smooth outer surface.
- The invention will be further described with reference to the accompanying drawings where like numbers refer to like parts in several views and wherein:
- FIG. 1 is a partial cross-sectional side view of an illustrative catheter shaft in accordance with the present invention;
- FIG. 2 is a cross-sectional side view of an illustrative strand used in forming the reinforcing member of FIG. 1;
- FIG. 3 is a partial cross-sectional side view of a reinforcing member passing through a heated die;
- FIG. 4 is a partial cross-sectional side view of an extruder extruding an outer layer over an illustrative reinforcing member;
- FIG. 5 is a partial cross-sectional side view of a reinforcing member enclosed in a heated die; and
- FIG. 6 is a partial cross-sectional side view of the reinforcing member of FIG. 5 after the heat and pressure are removed.
- FIG. 1 is a partial cross-sectional side view of an illustrative catheter shaft in accordance with the present invention. The catheter shaft is generally shown at10, and includes an inner tubular reinforcing
member 12 surrounded by anouter layer 14. The inner tubular reinforcingmember 12 is preferably formed from one ormore strands 16 that are wound or braided around amandrel 18. The outer diameter of themandrel 18 is sized to correspond to the desired inner diameter of the inner lumen of thecatheter shaft 10. When themandrel 18 is removed, the innertubular reinforcing member 12 defines the inner lumen of thecatheter shaft 10. - The
strands 16 of the reinforcing member can be wound in any pattern including a coil or braid pattern. A braid pattern is shown in the partial cut-awayregion 20 of FIG. 1. When a braid pattern is provided, it is contemplated that the braid angle may be adjusted to provide the desired flexibility to theshaft 10, and may be varied along the length of theshaft 10. In one embodiment, each strand of the braid or coil is a wire, such as a stainless steel wire. - Once the inner
tubular reinforcing member 12 is formed around themandrel 18,outer layer 14 is provided. Theouter layer 14 is preferably extruded over the outer surface of the innertubular reinforcing member 12. In some embodiments, it may be desirable to prevent theouter layer 14 from flowing through the innertubular reinforcing member 12, and to themandrel 18. In these embodiments, a tight braid pattern may be used when forming the innertubular reinforcing member 12. Once theouter layer 14 is provided, themandrel 18 is removed, leaving ahollow catheter shaft 10. Theouter layer 14 is preferably formed from polyester, polyether block amide, nylon, or some other thermoplastic polymer. - When additional lubricity is desired in the inner lumen of the
catheter shaft 10, each strand of the braid or coil may be a composite of aninner core wire 24 that is coated with apolymer 26, such as shown in FIG. 2. Thepolymer 26 may be used to increase the lubricity of the inner surface of the inner lumen of thecatheter shaft 10. As such, thepolymer 26 may be a lubricious polymer such as polytetrafluoroethylene (PTFE) or perfluoroalkoxy (PFA or MFA). PFA and MFA, both perfluoroalkoxy polymers, are available from Ausimont, S.P.A. Utilizing the above-described method of manufacture, when themandrel 18 is removed, the wound or braided polymer coatedcore wire 24 defines the inner lumen of thecatheter shaft 10. The polymer coating, as braided or wound, is exposed and will contact a device passed through the lumen, thus providing a lubricious surface which has a surface contour defined by the braid or coil pattern. Alternatively, or in addition to, thepolymer 26 may be used to provide a smooth inner surface to the inner lumen by modifying the above method, as further described below. - FIG. 3 is a partial cross-sectional side view of a reinforcing
member 30 that is being passed through aheated die 40. The reinforcingmember 30 includes one ormore strands 32 wound in a coil or braid pattern, as described above. Eachstrand 32 is shown having aninner core 34 made from stainless steel or the like with athermoplastic polymer coating 36. Thethermoplastic polymer coating 36 is preferably formed from a lubricious thermoplastic polymer such as a perfluoroalkoxy polymer. For applications where lubricity is not necessary, as in some diagnostic applications, any suitable thermoplastic polymer could be utilized. - To provide a relatively smooth inner surface to the catheter shaft, the reinforcing
member 30 is wound or braided on amandrel 38, which has a relatively smooth outer surface. The reinforcingmember 30, along with themandrel 38, is then passed throughheated die 40. The heated die 40 causes thethermoplastic polymer 36 to conform to the outer surface of themandrel 38 and the inner surface of theheated die 40. Thethermoplastic polymer 36 also tends to fill the interstitial sites between the windings of the braid or coil pattern. Accordingly, a thin-walled inner liner that is impregnated with the core wire windings is provided along the length of the catheter shaft. - The heat required to flow many thermoplastic polymers can be relatively low. As such, the
mandrel 38 need only be made from a material that has a flow temperature that is higher than the flow temperature of thethermoplastic polymer 36 used to coat thecore wires 34 of each strand of the reinforcing member. When the thermoplastic polymer of each strand is a perfluoroalkoxy polymer, for example, the mandrel may be made from an acetyl polymer. By using a polymer mandrel, rather than a copper or silver coated copper mandrel, the cost of the mandrel may be significantly reduced. In any event, an outer layer (not shown) is preferably extruded over thereinforcement member 30. - In another embodiment, the heat of the extrusion process of the outer layer is used to cause the thermoplastic polymer of the reinforcement layer to conform to the outer surface of the mandrel. Thus, a heated die may not be required. Such an embodiment is shown in FIG. 4. A
reinforcement member 50 is provided over a mandrel, as described above with respect to FIG. 3. Then, anouter layer 52 is extruded over thereinforcement member 50 usingextruder head 54. During the extrusion process, significant heat can be generated in the reinforcement member. Because the heat required to flow many thermoplastic polymers can be relatively low, it is contemplated that the heat from the extrusion process of theouter layer 52 may be sufficient to flow the thermoplastic polymer on the core wires of the reinforcingmember 50. - In some embodiments, it may be desirable to use a non-thermoplastic polymer such as PTFE to coat the core wires of the strands of the reinforcing member. Such non-thermoplastic polymers do not readily flow when subject to heat. For PTFE, both heat and pressure may be required to change the shape of the polymer, but even then, the PTFE may not flow like a thermoplastic polymer.
- FIG. 5 is a partial cross-sectional side view of a
heated die 60 applying heat and pressure to an illustrative reinforcingmember 62. In this illustrative embodiment, each strand of the reinforcingmember 62 has acore wire 64 formed from stainless steel or the like, which is coated with anon-thermoplastic polymer 66 such as PTFE. Like above, the reinforcingmember 62 is preferably wound around amandrel 68, as shown. Because of the relatively high heat and pressure required to change the shape of the PTFE polymer, the mandrel is preferably made from copper or silver coated copper. Other suitable mandrel materials can be used, for example, nylon coated stainless steel. - To shape the non-thermoplastic polymer that coats the core wires of the
reinforcement member 62, aheated die 60 is provided around at least a portion of the outer surface of the reinforcingmember 62. Theheated die 60 applies both heat and pressure to the reinforcingmember 66. The heat and pressure may cause thenon-thermoplastic polymer 66 to conform to the shape of the outside surface of themandrel 68 and the inside surface of theheated die 60. Once the non-thermoplastic polymer is properly formed, the result is a thin-walled reinforced non-thermoplastic tube around themandrel 68, as shown in FIG. 6. - An outer layer (not shown) may then be extruded over the reinforcing
member 62. To allow the outer layer to properly adhere to the reinforcingmember 62, it may be desirable to etch the outer surface of the reinforcingmember 62. Once etched, the outer layer may be extruded over the reinforcingmember 62. Again, the outer layer is preferably formed from polyester, polyether block amide, nylon or some other thermoplastic polymer. Once the outer layer is extruded, themandrel 68 is removed. - Although the present invention is described in terms of the preferred embodiment above, it should be noted that alterations and modifications of this invention will be possible without departing from the spirit and scope of this invention.
Claims (33)
1. A catheter shaft having an inner lumen extending therethrough, comprising:
an inner tubular braid member formed from one or more braided strands, the inner tubular braid member defining at least part of the inner lumen of the catheter shaft; and
an outer tubular member disposed over the inner tubular braid member.
2. A catheter according to claim 1 , wherein selected strands include an elongated inner core coated with a polymer.
3. A catheter according to claim 2 , wherein the inner core is formed from stainless steel.
4. A catheter according to claim 2 , wherein the polymer is a lubricious polymer.
5. A catheter according to claim 4 , wherein the polymer includes polytetrafluoroethylene (PTFE).
6. A catheter according to claim 4 , wherein the polymer is a perfluoroalkoxy polymer.
7. A catheter according to claim 1 , wherein the outer tubular member includes polyester.
8. A catheter according to claim 7 , wherein the outer tubular member is extruded over the inner tubular braid member.
9. A method for forming a catheter shaft, the method comprising the steps of:
winding one or more elongated strands around a mandrel, wherein selected strands have an inner core coated by a polymer, the wound elongated strands collectively forming an inner tubular reinforcing member;
providing an outer tubular member over the inner tubular reinforcing member; and
removing the mandrel.
10. A method according to claim 9 , wherein the one or more elongated strands are wound to form a braid.
11. A method according to claim 9 , wherein the providing step includes the step of extruding a polymer over the inner tubular reinforcing member to form the outer tubular member.
12. A method according to claim 10 , wherein the braid is wound in a pattern that substantially prevents the extruded polymer of the outer tubular member from flowing through the inner tubular reinforcing member to the mandrel.
13. A method according to claim 9 , wherein the one or more elongated strands are wound to form a coil.
14. A method according to claim 9 , wherein the inner core of selected strands is stainless steel.
15. A method according to claim 9 , wherein the polymer encasing the inner core of selected strands is a lubricious polymer.
16. A method according to claim 15 , wherein the lubricious polymer is polytetrafluoroethylene (PTFE).
17. A method according to claim 16 , wherein the mandrel comprises a copper core coated with silver.
18. A method according to claim 16 , further comprising the step of applying heat and pressure to the inner tubular reinforcing member before providing the outer tubular member.
19. A method according to claim 18 , wherein the applied heat and pressure is sufficient to cause the polytetrafluoroethylene (PTFE) polymer that coats the inner core of selected strands to substantially conform to the shape of the mandrel.
20. A method according to claim 15 , wherein the lubricious polymer is a perfluoroalkoxy polymer.
21. A method according to claim 20 , wherein the mandrel is formed from an acetyl polymer.
22. A method according to claim 20 , further comprising the step of applying heat to the inner tubular reinforcing member before providing the outer tubular member.
23. A method according to claim 22 , wherein the applied heat is sufficient to cause the perfluoroalkoxy polymer that coats the inner core of selected strands to flow and create a thin-walled liner adjacent the mandrel.
24. A method according to claim 22 , wherein the heat is provided by a heated die.
25. A method according to claim 22 , wherein the providing step includes the step of extruding a polymer over the inner tubular reinforcing member to form the outer tubular member.
26. A method according to claim 25 , wherein the heat is applied by the extrusion of the outer tubular member.
27. A method according to claim 9 , further comprising the step of etching an outer surface of the inner tubular reinforcing member before providing the outer layer.
28. A method for forming a catheter shaft, the method comprising the steps of:
winding one or more elongated strands around a mandrel having a relatively smooth outer surface, wherein selected strands have an inner core coated by a polymer, the wound elongated strands collectively forming an inner tubular reinforcing member;
applying heat to the inner tubular reinforcing member, wherein the heat is sufficient to cause the polymer that coats the inner core of selected strands to conform to the relatively smooth outer surface of the mandrel; and
removing the mandrel.
29. A method according to claim 28 , wherein the heat applying step further includes the step of applying inward pressure to the inner tubular reinforcing member toward the mandrel.
30. A method according to claim 28 , further comprising the step of providing an outer tubular member over the inner tubular reinforcing member.
31. A method according to claim 30 , further comprising the step of etching the outer surface of the inner tubular reinforcing member before providing the outer tubular member.
32. A method according to claim 30 , wherein the outer tubular member is provided by extruding a polymer over the inner tubular reinforcing member.
33. A method according to claim 32 , wherein the extruding step provides the heat for the heat applying step.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
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US10/701,699 US20040089969A1 (en) | 2000-08-03 | 2003-11-04 | Reinforced catheter and method of manufacture |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US09/631,800 US6669886B1 (en) | 2000-08-03 | 2000-08-03 | Reinforced catheter and method of manufacture |
US10/701,699 US20040089969A1 (en) | 2000-08-03 | 2003-11-04 | Reinforced catheter and method of manufacture |
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US09/631,800 Continuation US6669886B1 (en) | 2000-08-03 | 2000-08-03 | Reinforced catheter and method of manufacture |
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US20040089969A1 true US20040089969A1 (en) | 2004-05-13 |
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US09/631,800 Expired - Lifetime US6669886B1 (en) | 2000-08-03 | 2000-08-03 | Reinforced catheter and method of manufacture |
US10/701,699 Abandoned US20040089969A1 (en) | 2000-08-03 | 2003-11-04 | Reinforced catheter and method of manufacture |
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US09/631,800 Expired - Lifetime US6669886B1 (en) | 2000-08-03 | 2000-08-03 | Reinforced catheter and method of manufacture |
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US (2) | US6669886B1 (en) |
EP (1) | EP1305072B1 (en) |
JP (1) | JP4851680B2 (en) |
AT (1) | ATE294612T1 (en) |
CA (1) | CA2417701C (en) |
DE (1) | DE60110601T2 (en) |
WO (1) | WO2002011806A1 (en) |
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- 2001-05-30 CA CA2417701A patent/CA2417701C/en not_active Expired - Fee Related
- 2001-05-30 WO PCT/US2001/017353 patent/WO2002011806A1/en active IP Right Grant
- 2001-05-30 DE DE60110601T patent/DE60110601T2/en not_active Expired - Lifetime
- 2001-05-30 AT AT01939636T patent/ATE294612T1/en not_active IP Right Cessation
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Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20070005003A1 (en) * | 2003-12-31 | 2007-01-04 | Patterson Ryan C | Reinforced multi-lumen catheter |
US20100132879A1 (en) * | 2003-12-31 | 2010-06-03 | C.R. Bard, Inc. | Reinforced multi-lumen catheter |
US7972465B2 (en) | 2003-12-31 | 2011-07-05 | C. R. Bard, Inc. | Reinforced multi-lumen catheter |
US20110192008A1 (en) * | 2003-12-31 | 2011-08-11 | C. R. Bard, Inc. | Reinforced multi-lumen catheter |
US8430988B2 (en) | 2003-12-31 | 2013-04-30 | C. R. Bard, Inc. | Reinforced multi-lumen catheter |
US20060095050A1 (en) * | 2004-09-14 | 2006-05-04 | William A. Cook Australia Pty. Ltd. | Large diameter sheath |
US10426920B2 (en) | 2013-12-20 | 2019-10-01 | Boston Scientific Scimed, Inc. | Integrated catheter system |
US10610666B2 (en) | 2015-12-28 | 2020-04-07 | Covidien Lp | Multi-filament catheter |
US11844909B2 (en) | 2020-03-23 | 2023-12-19 | Boston Scientific Scimed, Inc. | Guide catheter with reinforcing member |
EP3995170A3 (en) * | 2020-11-06 | 2022-10-05 | DePuy Synthes Products, Inc. | Catheter braid wire with variable cross-section shape |
Also Published As
Publication number | Publication date |
---|---|
ATE294612T1 (en) | 2005-05-15 |
EP1305072A1 (en) | 2003-05-02 |
WO2002011806A1 (en) | 2002-02-14 |
DE60110601D1 (en) | 2005-06-09 |
CA2417701A1 (en) | 2002-02-14 |
US6669886B1 (en) | 2003-12-30 |
JP4851680B2 (en) | 2012-01-11 |
JP2004505687A (en) | 2004-02-26 |
CA2417701C (en) | 2010-06-29 |
DE60110601T2 (en) | 2005-10-06 |
EP1305072B1 (en) | 2005-05-04 |
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Legal Events
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AS | Assignment |
Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018505/0868 Effective date: 20050101 Owner name: BOSTON SCIENTIFIC SCIMED, INC.,MINNESOTA Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018505/0868 Effective date: 20050101 |
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STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |