US20110297307A1

US20110297307A1 - Unfused catheter body feature methods of manufacture

Info

Publication number: US20110297307A1
Application number: US13/211,399
Authority: US
Inventors: Robert R. Slazas; Jessica T. Schenck
Original assignee: Codman and Shurtleff Inc
Current assignee: DePuy Spine LLC; DePuy Synthes Products Inc
Priority date: 2006-08-23
Filing date: 2011-08-17
Publication date: 2011-12-08
Also published as: CA2598242A1; US8021352B2; EP1894594A1; US20080051761A1; CA2598242C; JP2008068076A; EP1894594B1

Abstract

The disclosure is directed to manufacturing tubular bodies for catheters. An inner tubular catheter body has an inner layer, a braided portion over the inner layer and an outer layer. The outer layer is fused to the braided portion for a selected length or lengths of the inner tubular body and is unfused for a selected length or lengths to achieve the desired combination of stiffness and flexibility.

Description

CROSS REFERENCE TO RELATED APPLICATION

This is a divisional of and claims priority from U.S. application Ser. No. 11/466,632, filed Aug. 23, 2006, Publication No. 2008/00511761, hereby incorporated by reference hereinto.

FIELD OF THE INVENTION

The disclosure relates to tubular bodies of catheters designed to deliver devices that are used to treat or diagnose defects in the vasculature. The tubular bodies of the catheters are enhanced in flexibility and bendability while exhibiting good column strength. Special application is found for inner catheter bodies, most particularly at distal locations of an inner catheter body.

BACKGROUND OF THE INVENTION

The intraluminal delivery of diagnostic catheters, treatment fluids, expansion devices or stents is commonly used to diagnose or treat defects, such as blockages and stenoses, within the human vasculature. Expansion devices can take a number of forms, including a balloon that is inflated to open the blockage. The use of a balloon may provide only a temporary solution and a stent may be inserted after or instead of the balloon as a more permanent solution.
When treating defects in peripheral, coronary or neural blood vessels, it is usually necessary to pass the treatment or diagnostic device through tortuous paths in the vasculature, and often through narrow constrictions, to reach the desired site. To accomplish this, the devices often are delivered by a catheter. Catheters generally have a tubular shaft with a lumen and may include an inner member. To guide the catheter through the vasculature to the desired site, catheters can be passed over a guidewire.
The parameters of trackability, pushability and crossability are often assessed when discussing catheter performance. An optimal design would allow the catheter to easily follow the path of the vasculature (trackability) and to readily traverse narrow constrictions in the vasculature (crossability) but would not substantially affect the ability to transmit force from the proximal end to the distal end of the catheter (pushability).
Trackability and crossability are improved by the properties of the most distal portion of the catheter: A flexible distal portion improves performance of the catheter with respect to these parameters. However, the catheter body must not be too flexible or pushability will be adversely affected. To attempt to reconcile these differing requirements, catheters have been designed that have a flexible distal portion but a stiffer proximal portion. However, these catheters often require elaborate designs that are difficult to manufacture. For example, Griffin et al., U.S. Pat. No. 7,001,369 describes a device that requires multiple reinforcement layers and the use of several types of materials to achieve the required properties. Other devices having catheter shaft variations are found in Jordan et al. U.S. Patent Application Publication No. 2005/0288628 and Sherman et al. U.S. Patent Application Publication No. 2006/0030835. Each patent or publication referred to is herein incorporated by reference.
A need remains for an effective but simple-to-use and easily manufactured catheter structure that allows for flexibility while maintaining adequate stiffness in important areas of the inner tubular body of the catheter. At times it is desired to have a catheter inner tubular body that allows for flexibility or stiffness in selected areas.

SUMMARY

In one embodiment, the disclosure is directed to catheters with inner tubular bodies where the inner tubular body has an inner layer, a braided portion extending over at least part of the inner layer and an outer layer that extends over the braided portion. The outer layer is fused to the braided portion for one or more selected lengths and is unfused to the braided portion for one or more other lengths.
In another embodiment, the disclosure is directed to catheters with inner tubular bodies where the inner tubular body has an inner layer, a braided portion extending over at least part of the inner layer and an outer layer that extends over the braided portion. The outer layer is fused to the braided portion for one or more selected lengths and is unfused to the braided portion for one or more other lengths, and the outer layer has the same composition over its entire length.
In another embodiment, the disclosure is directed to balloon catheters with inner tubular bodies where the inner tubular body has an inner layer, a braided portion extending over at least part of the inner layer and an outer layer that extends over the braided portion. The outer layer is fused to the braided portion for a length of the distal portion of the catheter and is unfused to the braided portion for over at least part of the length that the balloon overlies.
The disclosure is also directed to methods of manufacture of inner tubular bodies where an inner layer is applied to the surface of a mandrel, a braided portion is applied to the outside surface of said inner layer, an outer layer is applied around the braided portion and the inner layer and then one or more selected lengths of the outer layer is or are fused to the braided portion. One or more lengths remain unfused. The mandrel is removed to form a inner tubular member.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a medical device catheter;

FIG. 2 is a longitudinal cross-sectional view of a catheter including a braided tube assembly; and

FIG. 3 is a longitudinal cross-sectional view of a distal portion of catheter having a tubular inner body and a balloon component.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

As required, detailed embodiments of the present disclosure are presented herein; however, it is to be understood that the disclosed embodiments are merely exemplary, which may be embodied in various forms. Therefore, specific details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the embodiments of the disclosure in virtually any appropriate manner.
The disclosure relates to inner tubular bodies for catheters. In general, the inner tubular bodies have an inner layer that defines a lumen, a braided portion that extends over at least a portion of the inner layer and an outer layer that extends over the braided portion. The outer layer is fused to the braided portion for one or more selected lengths and is unfused for one or more selected lengths. The inner tubular bodies of the present disclosure may be used for catheters designed for peripheral, coronary or neurovascular applications.
FIG. 1 shows one embodiment of a catheter according to the disclosure. The catheter 10 has a long flexible tubular shaft 12 that extends from a proximal portion 15 to a distal end portion 16. A hub 14 is present at the proximal end of the shaft. Catheter 10 defines at least one passage or lumen 17.
FIG. 2 shows one embodiment of a cross-sectional view of a tubular body according to the disclosure. The tubular body 21, with proximal portion 19 and distal end portion assembly 20, generally has an inner layer 22 that defines a lumen 24, a braided portion 26 that extends over the inner layer, and an outer layer 28 that extends over the braided portion 26. According to the present disclosure, the outer layer 28 is fused to the braided portion 26 for a selected length 27 and is unfused for a selected length 29. The most distal portion 25 of the outer layer may also fused to the braided portion. Also, the outer layer typically will be fused to the inner layer at the fused length.
In a preferred embodiment, a selected length of the proximal portion of the outer layer is fused to the braided portion while a length of distal portion is unfused. In this and similar embodiments, the unfused distal portion has greater flexibility, allowing it to bend more easily and thereby facilitating its movement through the vasculature. For example, the braided portion components are more able to slide with respect to each other in the unfused portion. The fused proximal portion is stiffer and thereby facilitates the pushing of the catheter through the vasculature. In the fused portion, the braided portion components become relatively fixed due to fusion to the outer layer, resulting in a stiffer proximal portion.
FIG. 3 shows a cross-sectional view of one embodiment of a balloon catheter 30 according to the present disclosure. An inner tubular body 31 has a inner layer 32, a braided portion 33 and an outer layer 34 and defines a lumen 35. A balloon 36 is attached to the inner tubular body at its distal end along balloon distal leg 42, and the balloon is attached to an outer tubular body 37 at its proximal end along balloon proximal leg 43. The balloon may be composed of a variety of materials including those known in the art such as nylon, PEBAX or silicone urethanes. A second lumen 38 is defined by the annular space between the inner 31 and outer 37 tubular bodies.
In this embodiment, the fused length or region 39 of the outer layer 34 extends from the proximal portion of the catheter to the proximal end of the balloon. What is meant by the proximal end of the balloon can range from radially internal of the proximal end of the proximal leg 43 to the distal end of the proximal leg 43. For example, FIG. 3 shows (in solid lines) the fused length or region 39 extending distally to radially internal of the distal end of the proximal leg 43. Broken lines at this general location illustrate the unfused length extending proximally to radially internal near or beyond the proximal end of the proximal leg 43. In these illustrated embodiments, the unfused length or region 40 begins immediately distal of the distal end of the fused length or region 39.
It is contemplated that the illustrated transitions between these fused and unfused regions also can be positioned between or beyond these explicitly illustrated (in solid or broken lines) locations in this embodiment. Thus, in this embodiment, the unfused length or region 40 extends distally from proximally beyond, at or near the proximal end of the balloon to at or near the distal end of the balloon.
Each unfused portion or region allows for greater flexibility in this area of the balloon and helps compensate for reduced flexibility that may occur due to the presence of the balloon at this location, including when the balloon is deflated and covers the tubular member. The most distal portion of the outer layer may be fused to the braided portion such that the outer layer is held to the braid in this section by means of what may be referred to as ring fuse 41. It is convenient for such a ring fuse or the like to include the distal leg 42 of the balloon.
In a preferred embodiment, the outer layer 28, 34 may have the same composition over its entire length. Preferably, the material or materials selected for the outer layer have a Shore Durometer hardness value equal to or less than about 72 D. The material may have a Shore hardness value as soft as about 80 A. The Shore hardness can range from about 25 D to about 72 D. Suitable materials for the outer layer include but are not limited to polyamides, polyimides, nylons, polyethylenes, polyvinylidene fluoride (PVDF), polyesterether block amides, polyurethanes and combinations of these materials. Polyesterether block amides, sold under the Trademark PEBAX by Arkema Inc, are an especially preferred material. Another range of Shore hardness values for PEBAX is from about 35 D to about 55 D.
The braided portion of the tubular body may be formed from a range of materials. Optimally, the structure of the braided portion should not be compromised when the outer layer is fused to the braided portion. The braided portion may be made of wire made from metals such as platinum or stainless steel. The braided portion may also be made from fibers or filaments made from thermoplastic or thermoset materials. Examples of these include but are not limited to polyamides and liquid crystal polymers such as those sold under the trade name Vectra. The pic values for the braided portion are the range of from about 25 to about 140 pics/inch and preferably from about 60 to 120 pics/inch. A higher pic value affords greater flexibility to the tubular member. In one embodiment, the pic values may be constant over the length of the braided portion. In other embodiments, pic values may vary and consequently the flexibility of the braided portion may vary over the length of the braided portion.
The length, location and number of fused and unfused regions of the outer layer may be adjusted depending on the application. For example, an unfused region may be included in a region where it is necessary to have a braid with a low pic count because of a need to resist torsional strain or some other mechanical requirement. Thus, the inclusion of one or more unfused outer layer portions will increase flexibility in these regions.
An inner tubular member according to the disclosure may be made according to the following method. A core wire or mandrel serves as a foundation, around which the catheter shaft tube is built up. After the tube is fully formed, the mandrel is removed, leaving the inner catheter tubular member. The size of the core wire used for the mandrel will determine the size of the catheter shaft tube lumen, when the core wire is eventually removed. Various materials may be used for the mandrel, including stainless steel or copper, which may be silver-coated. By way of example only, the diameter of the wire/mandrel used to form the lumen for catheters used in neurovascular applications may be from about 0.010 inch to about 0.020 inch.
An inner layer is applied to the core wire by any of several methods: wire mandrel extrusion, dipping or spraying using solvents and/or heat to create a solution of the polymer material, fuse-down techniques such as those employing shrink tubing, or other deposition techniques. According to some embodiments of the present disclosure, the purpose of the inner polymer layer is to provide a lubricious inner surface for the lumen of the resulting tube, rather than to substantially contribute to the catheter shaft performance and structural properties. Accordingly, the inner polymer layer may be very thin, in the range of from about 0.0005 inch to about 0.002 inch. The inner layer may be formed from materials including but not limited to polytetrafluoroethylene (PTFE) expanded polytetrafluoroethylene (EPTFE) or high density polyethylene (HDPE).
The braided portion is added to the outside of the inner polymer layer. By way of example only, catheters used in neurovascular applications may have a braided portion in the range of thicknesses of about 0.0005 inch to about 0.003 inch.
The outer layer is then placed over the braided portion. The outer polymer layer may be in the range of from about 0.001 inch to 0.008 inch thick for catheters used in neurovascular applications. If the entire outer polymer layer has the same composition, then possible methods for adding the outer layer include: wire mandrel extrusion (in which the subassembly of coated core wire, inner polymer liner, and reinforcement act as a “wire mandrel”); dip coating or spraying using solvents and/or heat to create a solution of the material; or fuse-down techniques such as for example those employing shrink tubing. When heat is applied at selected lengths along the assembled tubular member, the outer layer material changes its form to fuse to the braided portion. The outer layer material may, for example, melt to fill or span the spaces between the braid components. Other methods known in the art than the application of heat may also be used to fuse the outer layer to the braided portion. The wire mandrel is then removed, leaving the desired composite catheter shaft tube.
It will be understood that the embodiments of the present invention which have been described are illustrative of some of the applications of the principles of the present disclosure. Numerous modifications may be made by those skilled in the art without departing from the true spirit and scope of the disclosure. Various features which are described herein can be used in any combination and are not limited to procure combinations that are specifically outlined herein.

Claims

1-25. (canceled)

26. A method of manufacture of a tubular member for a catheter, comprising:

(a) providing a mandrel;

(b) applying an inner layer of a first polymer to the surface of the mandrel;

(c) applying a braided portion to the outside surface of the inner layer;

(d) applying an outer layer of a second polymer around the braided portion and the inner layer;

(e) fusing at least one selected length of the outer layer to the braided portion to form a fused region of the tubular member while refraining from fusing at least one selected length of the outer layer to the braided portion to provide an unfused region; and

(f) removing the mandrel to provide the tubular member.

27. The method of claim 26 wherein the inner and outer layers are applied by an extrusion process, and said fusing includes fusing the inner layer to the outer layer at the fused region.

28. The method of claim 26 wherein said applying the outer layer applies the same polymer material of the same material hardness and said fusing provides the unfused area as a selected length of the distal end portion of the flexible shaft, and the remainder of the outer layer is the fused region.

29. The method of claim 26 wherein said fusing fuses together the outer layer, braided portion and inner layer at the fused region.

30. The method of claim 26 wherein the second polymer of said fusing step said outer layer is a material selected from the group consisting of polyamides, polyimides, nylons, polyethylenes, PVDF, polyesterether block amides, polyurethanes and combinations thereof.

31. The method of claim 26 wherein the material of said fusing step outer layer has a Shore durometer hardness of not greater than about 72 D.

32. The method of claim 26 wherein the material of said fusing step outer layer has a Shore durometer hardness of from about 25 D to about 60 D.

33. The method of claim 26 wherein the material of said fusing step outer layer has a Shore durometer hardness of from about 35 D to about 55 D.

34. The method of claim 26 wherein the first polymer of said fusing step inner layer is formed from a material selected from the group consisting of polytetrafluoroethylene (PTFE), expanded polytetrafluoroethylene (EPTFE) and high density polyethylene (HDPE).

35. The method of claim 26 wherein said applying step applies the braided portion to a pic count of from about 25 to about 140 pics/inch.

36. The method of claim 26 wherein said applying step applies the braided portion to a pic count of from about 60 to about 120 pics/inch.

37. The method of claim 26 wherein said fusing provides an unfused region having a defined radius and a defined length along which the braided portion and the outer layer are unfused to each other and are unfused to any and all other members along the defined length.

38. The method of claim 26 further comprising fixing a balloon to the tubular body along at least a portion of the length of the unfused region and radially external of the unfused region.

39. The method of claim 38 wherein said fusing extends the unfused region longitudinally beyond the balloon.

40. The method of claim 38 wherein said fusing provides the outer layer with a proximal end portion and a distal end portion, the outer layer being fused to the braided portion and to the inner layer for a selected length to define the fused region, and the fused region and unfused region are made of the same polymer material, wherein the unfused region is a selected length of the distal end portion of the tubular body, and the remainder of the outer layer is the fused region.

41. A method of manufacture of a balloon catheter, comprising:

(a) providing a mandrel;

(b) applying an inner layer of a first polymer to the surface of the mandrel;

(c) applying a braided portion to the outside surface of the inner layer;

(e) fusing at least one selected length of the outer layer to the braided portion to form a fused region of the tubular member while refraining from fusing at least one selected length of the outer layer to the braided portion to provide an unfused region thereby providing an inner tubular body;

(f) positioning a flexible shaft coaxial with the inner tubular member, the flexible shaft having a proximal portion and distal end portion, the shaft defining a lumen within which the inner tubular body is positioned, the tubular body including a distal end portion and an outer layer with a proximal and distal end;

(g) providing a balloon member having a proximal leg and a distal leg;

(h) securing the proximal leg of the balloon member to the distal end portion of the flexible shaft;

(i) securing the distal leg of the balloon member to the distal end portion of the tubular body;

(j) positioning the unfused length at a location radially inward of at least a portion of the balloon between the proximal leg and the distal leg of the balloon; and

(k) removing the mandrel upon formation of the inner tubular body or thereafter.

42. The balloon catheter manufacturing method of claim 41 wherein said positioning results in the unfused length extending substantially the entire length of the balloon.

43. The balloon catheter manufacturing method of claim 41 wherein said positioning results in the unfused length comprising one or more unfused lengths and extending between approximately the proximal end of the proximal leg of the balloon member to the proximal end of the distal leg of the balloon member.

44. The balloon catheter manufacturing method of claim 41 wherein said positioning results in the unfused length extending proximally of the proximal end of the distal leg of the balloon member.