U.S. patent application number 11/040704 was filed with the patent office on 2005-06-09 for method of making an expandable medical device formed of a compacted porous polymeric material.
Invention is credited to Blankenship, Delma M., Gonzalez, Fernando, Sridharan, Srinivasan.
Application Number | 20050121824 11/040704 |
Document ID | / |
Family ID | 34215701 |
Filed Date | 2005-06-09 |
United States Patent
Application |
20050121824 |
Kind Code |
A1 |
Gonzalez, Fernando ; et
al. |
June 9, 2005 |
Method of making an expandable medical device formed of a compacted
porous polymeric material
Abstract
A method of making a catheter balloon or other expandable
tubular medical device or component thereof formed of a compacted
porous polymeric material, in which a tube of porous polymeric
material is axially compacted, preferably without increasing the
outer diameter of the tube, by positioning heat shrink material on
the porous polymeric tube and heating the heat shrink material to
decrease the length and diameter of the heat shrink material.
Inventors: |
Gonzalez, Fernando;
(Campbell, CA) ; Sridharan, Srinivasan; (Morgan
Hill, CA) ; Blankenship, Delma M.; (Sunnyvale,
CA) |
Correspondence
Address: |
FULWIDER PATTON LEE & UTECHT, LLP
HOWARD HUGHES CENTER
6060 CENTER DRIVE
TENTH FLOOR
LOS ANGELES
CA
90045
US
|
Family ID: |
34215701 |
Appl. No.: |
11/040704 |
Filed: |
January 20, 2005 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11040704 |
Jan 20, 2005 |
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10326333 |
Dec 19, 2002 |
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6863757 |
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Current U.S.
Class: |
264/230 ;
264/288.4; 264/288.8; 264/289.6; 264/291; 264/321 |
Current CPC
Class: |
B29L 2031/7542 20130101;
B29C 61/006 20130101; B29C 2791/001 20130101; B29K 2023/0683
20130101; B29K 2105/258 20130101; B29C 2049/4655 20130101; B29K
2027/18 20130101; B29C 2049/0089 20130101 |
Class at
Publication: |
264/230 ;
264/288.4; 264/288.8; 264/291; 264/289.6; 264/321 |
International
Class: |
B29C 055/22; B29C
061/02 |
Claims
1. A method of making a tubular medical device or component formed
of a compacted porous polymeric material, comprising: a)
longitudinally stretching a polymeric tube to a lengthened
configuration on a tubular layer of porous polymeric material, with
a mandrel in a lumen of the porous polymeric layer; b) axially
compacting the porous polymeric layer without increasing the outer
diameter of the porous polymeric layer, by transforming the
polymeric tube on the porous polymeric layer from the lengthened
configuration to a second configuration having a length shorter
than the lengthened configuration; and c) removing the polymeric
tube from the compacted porous polymeric layer and removing the
compacted porous polymeric layer from the mandrel, to form a
compacted porous polymeric layer of an expandable tubular medical
device or component having at least one layer.
2-7. (canceled)
8. The method of claim 1 wherein transforming the polymeric tube
from the lengthened configuration to the second configuration
comprises shortening the lengthened configuration length of the
polymeric tube by about 10 to about 70%.
9. The method of claim 8 wherein the axially compacted porous
polymeric layer has an axial compaction of about 10 to about
50%.
10-19. (canceled)
20. The method of claim 1 wherein the polymeric tube has an
original pre-longitudinally stretched length prior to being
longitudinally stretched to the stretched configuration, and a)
comprises longitudinally stretching the tube by about 1 to about
50% of the original pre-longitudinally stretched length of
polymeric tube.
21. The method of claim 20 wherein b) comprises the polymeric tube
returning to the original pre-longitudinally stretched length the
polymeric tube
22. A method of making a catheter balloon, comprising: a)
longitudinally stretching a polymeric tube to a lengthened
configuration on a tubular layer of porous polymeric material, with
a mandrel in a lumen of the porous polymeric layer; b) axially
compacting the porous polymeric layer without increasing the outer
diameter of the porous polymeric layer, by transforming the
polymeric tube on the porous polymeric layer from the lengthened
configuration to a second configuration having a length shorter
than the lengthened configuration; c) removing the polymeric tube
from the compacted porous polymeric layer and removing the
compacted porous polymeric layer from the mandrel, to form a
compacted porous polymeric layer; and d) securing a liner to the
compacted porous polymeric layer to form the catheter balloon.
Description
BACKGROUND OF THE INVENTION
[0001] This invention generally relates to medical devices, and
particularly to intracorporeal devices for therapeutic or
diagnostic uses such as balloon catheters, and vascular grafts.
[0002] In percutaneous transluminal coronary angioplasty (PTCA)
procedures, a guiding catheter is advanced until the distal tip of
the guiding catheter is seated in the ostium of a desired coronary
artery. A guidewire, positioned within an inner lumen of a
dilatation catheter, is first advanced out of the distal end of the
guiding catheter into the patient's coronary artery until the
distal end of the guidewire crosses a lesion to be dilated. Then
the dilatation catheter having an inflatable balloon on the distal
portion thereofis advanced into the patient's coronary anatomy,
over the previously introduced guidewire, until the balloon of the
dilatation catheter is properly positioned across the lesion. Once
properly positioned, the dilatation balloon is inflated with fluid
one or more times to a predetermined size at relatively high
pressures (e.g. greater than 8 atmospheres) so that the stenosis is
compressed against the arterial wall to open up the passageway.
Generally, the inflated diameter of the balloon is approximately
the same diameter as the native diameter of the body lumen being
dilated so as to complete the dilatation but not overexpand the
artery wall. Substantial, uncontrolled expansion of the balloon
against the vessel wall can cause trauma to the vessel wall. After
the balloon is finally deflated, blood flow resumes through the
dilated artery and the dilatation catheter can be removed
therefrom.
[0003] In such angioplasty procedures, there may be restenosis of
the artery, i.e., reformation of the arterial blockage, which
necessitates either another angioplasty procedure or some other
method of repairing or strengthening the dilated area. To reduce
the restenosis rate and strengthen the dilated area, physicians
frequently implant a stent inside the artery at the site of the
lesion. Stents may also be used to repair vessels having an intimal
flap or dissection or to generally strengthen a weakened section of
a vessel. Stents are usually delivered to a desired location within
a coronary artery in a contracted condition on a balloon of a
catheter which is similar in many respects to an angioplasty
balloon catheter, and expanded to a larger diameter by expansion of
the balloon. The balloon is deflated to remove the catheter and the
stent left in place within the artery at the site of the dilated
lesion. Stent covers commonly provided on an inner or an outer
surface of the stent have been used in, for example, the treatment
of pseudo-aneurysms and perforated arteries and to prevent prolapse
of plaque, and generally comprise a cylindrical tube of synthetic
or natural material. Similarly, vascular grafts comprising
cylindrical tubes commonly made from tissue or synthetic materials
such as polyester, expanded polytetrafluoroethylene, and DACRON,
are configured to be implanted in vessels to strengthen or repair
the vessel, or used in an anastomosis procedure to connect vessel
segments together.
[0004] In the design of catheter balloons, characteristics such as
strength, compliance, and profile of the balloon are carefully
tailored depending on the desired use of the balloon catheter, and
the balloon material and manufacturing procedure are chosen to
provide the desired balloon characteristics. A variety of polymeric
materials are conventionally used in catheter balloons. Use of
polymeric materials such as PET that do not stretch appreciably
consequently necessitates that the balloon is formed by blow
molding, and the deflated balloon material is folded around the
catheter shaft in the form of wings, prior to inflation in the
patient's body lumen. However, it can be desirable to employ
balloons, referred to as formed-in-place balloons, that are not
folded prior to inflation, but which instead readily expand to the
working diameter within the patient's body lumen from a generally
cylindrical or tubular shape (i.e., essentially no wings) that
conforms to the catheter shaft.
[0005] Catheter balloons formed of expanded polytetrafluoroethylene
(ePTFE) expanded in place within the patient's body lumen without
blow molding the ePTFE tubing have been disclosed. Prior disclosed
methods of forming the ePTFE balloon involve wrapping a sheet of
ePTFE on a mandrel and then heating the wrapped sheet to fuse the
layers of wrapped material together. However, one difficulty has
been further processing the resulting ePTFE tube after the layers
of wrapped material are fused together without damaging the ePTFE
tube.
SUMMARY OF THE INVENTION
[0006] This invention is directed to a method of making a catheter
balloon or other expandable tubular medical device or component
thereof formed of a compacted porous polymeric material, in which a
tube of porous polymeric material is axially compacted by
positioning heat shrink material on the porous polymeric tube, and
heating the heat shrink material to decrease the length and
diameter of the heat shrink material. Preferably, the heat shrink
material axially compacts the porous polymeric tube without
increasing the outer diameter of the porous polymeric tube.
[0007] The method of the invention generally comprises positioning
heat shrink material on a tube of porous polymeric material with a
mandrel in the porous polymeric tube lumen, and shrinking the heat
shrink material by heating the heat shrink material on the porous
polymeric tube. The heat shrink material shrinks axially to compact
the porous polymeric tube, and shrinks radially to radially
restrain the outer diameter of the porous polymeric tube during the
axial compaction. Thus, the outer diameter of the porous polymeric
tube preferably does not increase during the axial compaction. As a
result, the porous polymeric tube compacts uniformly and without
buckling or bunching, which provides an improved compacted porous
polymeric tube. The compacted porous polymeric tube is removed from
the mandrel, typically after the shrunk material is removed
therefrom, to form a layer of an expandable medical device or
component. In one embodiment, the resulting compacted porous
polymeric layer is then bonded to a second layer or liner, to form
a multilayered expandable medical device or component such as a
balloon for a catheter. By preventing or minimizing buckling or
other surface irregularities during compaction, the method of the
invention facilitates securely bonding the resulting compacted
porous polymeric tube to the second layer. Additionally, the method
of the invention provides uniform percent compaction of the porous
polymer tube, unlike methods in which the amount of compaction
varies along the length of the tube due to buckling in the tube
during the compaction process.
[0008] The heat shrink material of the invention has a desired
amount of axial shrinking and radial shrinking during the heating
thereof while on the porous polymeric tube. The heat shrink
material shrinks axially and radially to longitudinally compact the
underlying porous tube over the entire length of the porous tube
while providing the necessary force in the radial direction to
prevent radial growth of the porous polymeric tube. The amount of
axial or radial shrinking is expressed as a percentage of the
original length or diameter, respectively, prior to heating the
heat shrink material. The resulting amount of longitudinal
compaction produced in the porous tube is expressed herein as a
percentage length reduction. Thus, a porous polymeric tube having a
precompaction length (i.e., the length of the tube just prior to
being longitudinally compacted in accordance with the invention) of
2 cm, which is subsequently longitudinally compacted to a length of
1 cm, has a longitudinal compaction of 50% (i.e., (2 cm-1 cm).div.2
cm). In one presently preferred embodiment, the heat shrink
material axially heat shrinks by about 15 to about 50%, to produce
a compacted porous polymeric tube having a longitudinal compaction
of about 15 to about 50%.
[0009] In one embodiment, the heat shrink material positioned on
the porous polymeric tube comprises a tube of cross-linked
polymeric material which has been radially expanded and heated in
the radially expanded configuration. The radially expanded tube is
positioned on the porous polymeric tube preferably by
longitudinally stretching the radially expanded tube down onto the
porous polymeric tube. The cross-linked polymeric tube,
longitudinally and radially expanded from an original length and
diameter, will heat shrink back to the original length and diameter
as a result of the cross-linking plastic memory features.
Consequently, the cross-linked tube can be longitudinally stretched
and radially expanded by a specific amount to provide a heat shrink
tube which axially and radially shrinks by a desired amount during
heating. Unlike conventional commercially available heat shrink
tubing which is typically manufactured to maximize the amount of
radial shrinkage and minimize the amount of longitudinal shrinkage,
the heat shrink tube of the invention provides a desired large
amount of axial shrinking and typically a relatively small amount
of radial shrinking. In one embodiment, the heat shrink tube of
expanded cross-linked material axially heat shrinks by about 15 to
about 50% and radially heat shrinks by about 30 to about 60%, to
produce a compacted porous polymeric tube having a longitudinal
compaction of about 15 to about 50% and radial compaction of about
27 to about 40%. A variety of suitable commercially available
cross-linked polymeric material may be used, including in one
preferred embodiment a low density polyethylene (LDPE) such as
linear low density polyethylene (LLDPE). Preferably, the
cross-linked tube has a wall thickness which is not less than a
minimum wall thickness required to provide improved uniform
compaction without producing a wrinkled or buckled compacted porous
tube, which in one embodiment is a minimum wall thickness of about
0.004 inches.
[0010] In another embodiment, the heat shrink material positioned
on the porous polymeric tube comprises a sheet of biaxially
oriented heat shrink material wrapped around the porous polymeric
tube at least one time, and typically multiple times. The biaxial
(i.e., radial and axial) orientation provides the heat shrink
material with radial and axial shrinkage during heat shrinking
thereof. In one embodiment, the biaxially oriented heat shrink
material wrapped or otherwise positioned on the porous polymeric
tube axially heat shrinks by about 10 to about 70%, and more
specifically by about 10 to about 50%, and radially heat shrinks by
about 10 to about 70%, and more specifically by about 10 to about
50%, to produce a compacted porous polymeric tube having a
longitudinal compaction of about 10 to about 70%, and more
specifically about 10 to about 50%, and radial compaction of about
1 to about 40%. A variety of suitable commercially available
biaxially oriented heat shrink material may be used including
polyolefins such as CLYSAR available from Bemis, and heat shrink
tubing available from 3M.
[0011] In a presently preferred embodiment, the porous polymeric
material is selected from the group consisting of expanded
polytetrafluoroethylene (ePTFE), an ultra high molecular weight
polyolefin including ultra high molecular weight polyethylene,
porous polyolefins including polyethylene and polypropylene, and
porous polyurethane. In one embodiment, the porous material has a
node and fibril microstructure. ePTFE and ultra high molecular
weight polyethylene (also referred to as "expanded ultra high
molecular weight polyethylene") typically have a node and fibril
microstructure, and are not melt extrudable. The node and fibril
microstructure, when present, is produced in the porous material
using conventional methods, and the tube of porous polymeric
material preferably has the desired microstructure (e.g., porous
and/or node and fibril) before the heat shrink material is
positioned thereon. However, a variety of suitable porous polymeric
materials can be used in the method of the invention including
conventional catheter balloon materials which are melt extrudable.
In one presently preferred embodiment, the porous polymeric
material cannot be formed into a balloon by conventional balloon
blow molding, and is formed into a balloon by bonding a sheet of
the porous polymeric material together to form a tubular member,
and preferably provided with a nonporous second layer or liner to
form an inflatable balloon. The porous polymeric tube is typically
formed by wrapping a sheet of porous polymeric material on a
mandrel and heating the wrapped sheet to fuse sections of the sheet
together.
[0012] The compaction of the porous polymeric tube, in accordance
with the method of the invention using heat shrink material,
preferably imparts desired performance characteristics in the
resulting device or component. In one embodiment, the heat shrink
material compacts the porous polymeric tube to produce a balloon or
other device or component having improved dimensional stability and
a specific desired compliance curve during inflation of the
balloon. For example, in one embodiment the compaction produces a
balloon with a controlled length by controlling the axial
shortening or growth and the diameter growth of the balloon.
[0013] In a presently preferred embodiment, the tubular medical
device or medical device tubular component is an inflatable balloon
for a catheter. A balloon formed according to the method of the
invention can be used on a variety of suitable balloon catheters
including coronary and peripheral dilatation catheters, stent
delivery catheters, drug delivery catheters and the like. Although
discussed below primarily in terms of the embodiment in which the
medical device tubular component is an inflatable member such as a
balloon for a catheter, it should be understood that other
expandable medical devices and components are included within the
scope of the invention including stent covers and vascular
grafts.
[0014] The method of the invention provides for improved
manufacture of a compacted porous polymeric tube for use in an
expandable medical device or component. The porous polymeric tube
is uniformly compacted a desired amount without buckling as it is
longitudinally compacted by the heat shrink material therearound.
Moreover, the heat shrink material is easy to apply and remove from
the porous polymeric tube without damaging the porous polymeric
tube, for improved manufacturability and reduced damage to the
compacted tube. These and other advantages of the invention will
become more apparent from the following detailed description and
accompanying exemplary figures.
BRIEF DESCRIPTION OF THE DRAWINGS
[0015] FIG. 1A illustrates, partially in section, an assembly of a
porous polymeric tube on a mandrel with a tube of heat shrink
material on the porous polymeric tube, after the heat shrink tube
is heated to compact the porous polymeric tube in a method
embodying features of the invention.
[0016] FIG. 1B is a transverse cross sectional view of the assembly
shown in FIG. 1A, taken along line 1B-1B.
[0017] FIG. 2A is a longitudinal cross section of the heat shrink
tube of FIG. 1A before being radially expanded and placed around
the porous polymeric tube of FIG. 1A, with the radially expanded
heat shrink tube illustrated in dashed lines.
[0018] FIG. 2B is a transverse cross sectional view of the assembly
shown in FIG. 2A, taken along line 2B-2B.
[0019] FIG. 3A is an elevational view, partially in section, of the
heat shrink tube of FIG. 2A after being radially expanded and
positioned on the tube of porous polymeric material, and prior to
being longitudinally stretched on the porous polymeric tube, with
the longitudinally stretched heat shrink tube illustrated in dashed
lines.
[0020] FIG. 3B is a transverse cross sectional view of the assembly
shown in FIG. 3A, taken along line 3B-3B.
[0021] FIG. 4 is an elevational view, partially in section, of the
heat shrink tube of FIG. 3A after being longitudinally stretched on
the porous polymeric tube, and prior to being heated to heat shrink
and thereby compact the porous polymeric tube.
[0022] FIG. 5 illustrates an alternative embodiment in which the
heat shrink material is a sheet of biaxially oriented polymeric
material with the porous polymeric tube on a mandrel rolled
therein.
[0023] FIG. 6 is an elevational view, partially in section, of a
stent delivery balloon catheter having a balloon with an outer
layer formed of a compacted porous polymeric layer formed according
to a method which embodies features of the invention.
DETAILED DESCRIPTION OF THE INVENTION
[0024] FIG. 1A illustrates a compacted tube 10 formed of porous
polymeric material tube on a mandrel 12, after a tube 14 of heat
shrink material has been heated to shrink the tube 14 and thereby
compact the porous polymeric tube 10, in a method of making a
tubular medical device of component formed of the compacted porous
polymeric tube 10, embodying features of the invention. FIG. 1B is
a transverse cross sectional view of the assembly of FIG. 1A, taken
along line 1B-1B.
[0025] In the method of FIG. 1A, the heat shrink tube 14 is a tube
of cross-linked polymeric material which has been radially expanded
before being positioned on the porous polymeric tube 10, and then
positioned on the porous polymeric tube 10 and longitudinally
stretched down onto the porous polymeric tube 10 prior to being
heat shrunk thereon to compact the porous polymeric tube 10. FIG.
2A illustrates the cross-linked polymeric tube 14(a) prior to being
radially expanded, with the radially expanded cross-linked
polymeric tube 14(b) illustrated in dashed lines in FIG. 2A. In a
presently preferred embodiment, the cross-linked polymeric material
of tube 14(a) is polyethylene, although a variety of suitable
cross-linked polymers may be used including polypropylene,
polytetrafluoroethylene (PTFE), and PVC. The cross-linked polymeric
tube 14(a) has a wall thickness of about 0.01 to about 0.09 inches,
preferably about 0.05 to about 0.06 inches. The cross-linked
polymeric tube 14(a) is radially expanded to provide the desired
amount of radial shrinkage during heating thereof on the porous
polymeric tube 10. The cross-linked polymeric tube 14(a) is
typically radially expanded by about 30 to about 90% of the
original diameter to form radially expanded cross-linked polymeric
tube 14(b). Specifically, in one embodiment in which the original
inner diameter of the cross linked polymeric tube 14(a) is about
0.01 to about 0.03 inches, the tube 14(a) is radially expanded to
an inner diameter of about 0.04 to about 0.07 inches. The tube
14(a) can be radially expanded using a variety of suitable methods.
The tube 14(a) is typically radially expanded pressurizing the
interior of the tube, as for example by blow molding the tube 14(a)
by heating the tube 14(a) in a mold and introducing an inflation
medium such as a gas or liquid into the interior of the tube to
radially expand the tube 14(a). FIG. 2B is a transverse cross
sectional view of the assembly of FIG. 2A, taken along line
2B-2B.
[0026] The radially expanded cross-linked polymeric tube 14(b) is
then positioned on the tube 10 of porous polymeric material to be
compacted. FIG. 3A illustrates the radially expanded cross-linked
polymeric tube 14(b) positioned on the tube of porous polymeric
material with mandrel 12 in the lumen of the tube 10. The tube
14(b) is then longitudinally stretched down onto the porous
polymeric tube 10 to provide the desired amount of axial shrinkage
during heating thereof on the porous polymeric tube 10. The
cross-linked polymeric tube 14(b) is typically longitudinally
stretched, i.e., axially elongated, by about 1 to about 50% of the
original length of tube 14(b), to form longitudinally stretched and
radially expanded cross-linked polymeric tube 14(c) (see FIG. 4).
Specifically, in one embodiment, the tube 14(b) is longitudinally
stretched to a length of about 10 to about 20 cm to form tube
14(c). The tube 14(b) can be longitudinally stretched using a
variety of suitable methods, and is preferably longitudinally
stretched by being pulled at either end. The tube 14(b) is
typically longitudinally stretched at an elevated temperature of
about 200 to about 300.degree. F., to form tube 14(c). FIG. 3B is a
transverse cross sectional view of the assembly of FIG. 3A, taken
along line 3B-3B.
[0027] FIG. 4 illustrates the longitudinally stretched and radially
expanded tube 14(c) on the porous polymeric tube 10 and mandrel 12
therein, prior to heat shrinking the tube 14(c) to compact the
porous polymeric tube 10. Although not illustrated in FIG. 4, the
tube 14(c) is typically fixed in the stretched configuration by
attaching fixing members such as ties or clamps (not shown) on the
ends of the longitudinally stretched tube 14(c). The longitudinally
stretched and radially expanded tube 14(c) around the porous
polymeric tube 10 typically has a wall thickness of about 0.004 to
about 0.02 inches, preferably about 0.01 to about 0.015 inches. The
tube 14(c) is heated to an elevated temperature at or above the
glass transition temperature of the cross-linked or partially
cross-linked polymer to heat shrink the tube 14(c) and thereby
compact the porous polymeric tube 10, to form the compacted tube 10
as illustrated in FIG. 1. In a presently preferred embodiment, the
assembly illustrated in FIG. 4 is heated using a heating nozzle
traversed along and around the outer surface of the heat shrink
tube 14(c). However, a variety of suitable heating methods may be
used including heating in an oven. The tube 14(c) typically axially
shrinks back to the original pre-longitudinally stretched length,
and radially shrinks back to the original pre-radially expanded
diameter. In a presently preferred embodiment, the tube axially
heat shrinks by about 10 to about 50%, and radially heat shrinks by
about 10 to about 50%, to produce a compacted porous polymeric tube
10 having a longitudinal compaction of about 10 to about 50% and a
radial compaction of about 5 to about 15%.
[0028] FIG. 5 illustrates an alternative embodiment in which the
porous polymeric tube 10 is compacted using heat shrink material
comprising a sheet of biaxially oriented heat shrink polymeric
material 24 wrapped around the tube 10 on mandrel 12. FIG. 5
illustrates the porous polymeric tube 10 on mandrel 12 being rolled
in the sheet of heat shrink material 24, so that multiple layers of
heat shrink material are provided around the tube 10. Increasing
the number of layers of heat shrink material increases the
compression force provided by the heat shrink material during heat
shrinking thereof. In a presently preferred embodiment, the heat
shrink sheet 24 is wrapped around the porous polymeric tube 10
about 5 to about 20 times (to provide the same number of layers of
heat shrink material therearound). In a presently preferred
embodiment, the biaxially oriented heat shrink material forming
sheet 24 is a polyolefin such as CLYSAR, although a variety of
suitable heat shrink polymers may be used including polypropylene,
PTFE, PVC, and copolymers of polyolefins. The wall thickness of the
heat shrink sheet 24 prior to being heat shrunk is typically about
0.004 to about 0.01 inches, or about 75 to about 200 gauge. The
heat shrink sheet 24 is wrapped around the porous polymeric tube 10
so that the ends of the wrapped sheet 24 extend beyond the ends of
the tube 10 and onto the mandrel 12. In the embodiment illustrated
in FIG. 5, the heat shrink sheet 24 has a width longer than the
length of the porous polymeric tube 10, so that the sheet 24 covers
the tube 10. However, in an alternative embodiment (not shown), the
sheet 24 has a width not greater than the length of the tube 10, so
that the sheet 24 must be spirally wrapped along the length of the
tube 10 to fully cover the tube 10. The wrapped sheet 24 is heated
to an elevated temperature at or above the glass transition
temperature of the heat shrink polymer to heat shrink the wrapped
sheet 24 and thereby compact the porous polymeric tube 10, to form
the compacted tube 10 as discussed above in relation to the
embodiment of FIG. 4. In a presently preferred embodiment the
wrapped sheet 14 axially heat shrinks by about 30 to about 90%, and
radially heat shrinks by about 10 to about 50%, to produce a
compacted porous polymeric tube 10 having a longitudinal compaction
of about 5 to about 30% and a radial compaction of about 0 to about
10%.
[0029] The porous polymeric tube 10 may be processed prior to being
longitudinally compacted in accordance with the invention. For
example, in one embodiment, the tube 10 is preferably
longitudinally stretched prior to being longitudinally compacted by
the heat shrink tube 14 or wrapped heat shrink sheet 24.
[0030] The thus compacted porous polymeric tube 10 is removed from
the mandrel 12, before or after the heat shrunk tube 14 or wrapped
sheet 24 is removed therefrom. The compacted porous polymeric tube
10 may be further processed to form the completed tubular medical
device or component. For example, in one embodiment in which the
compacted porous polymeric tube forms a layer of a catheter
multilayered balloon, the compacted porous polymeric tube is
secured to or otherwise combined with a nonporous second layer to
form the multilayered balloon.
[0031] FIG. 6 illustrates an over-the-wire type stent delivery
balloon catheter 50 embodying features of the invention, having a
balloon formed according to a method of the invention. Catheter 50
generally comprises an elongated catheter shaft 52 having an outer
tubular member 53 and an inner tubular member 54. Inner tubular
member 54 defines a guidewire lumen 55 configured to slidingly
receive a guidewire 56, and the coaxial relationship between outer
tubular member 53 and inner tubular member 54. defines annular
inflation lumen 57. An inflatable balloon 58 disposed on a distal
section of catheter shaft 52 has a proximal skirt section sealingly
secured to the distal end of outer tubular member 53 and a distal
skirt section sealingly secured to the distal end of inner tubular
member 54, so that its interior is in fluid communication with
inflation lumen 57. An adapter 60 at the proximal end of catheter
shaft 52 is configured to provide access to guidewire lumen 55, and
to direct inflation fluid through arm 61 into inflation lumen 57.
FIG. 1 illustrates the balloon 58 prior to complete inflation, with
an expandable stent 62, having a tubular cover 63 thereon, mounted
on a working length of the balloon 58. The distal end of the
catheter may be advanced to a desired region of a patient's body
lumen 64 in a conventional manner, and balloon 58 inflated to
expand the covered stent 62, and the balloon deflated, leaving
covered stent 62 implanted in the body lumen 64.
[0032] In the embodiment illustrated in FIG. 1, balloon 58 has a
first layer 66 and a second layer 67. In a presently preferred
embodiment, the balloon 58 first layer 66 comprises a
fluoropolymeric material, which in one embodiment is a porous
fluoropolymeric material, and preferably a microporous
fluoropolymeric material having a node and fibril microstructure,
such as ePTFE. In the embodiment illustrated in FIG. 1, first layer
66 is formed of ePTFE, and the second layer 67 is formed of a
polymeric material preferably different from the polymeric material
of the first layer 66. Although discussed below in terms of one
embodiment in which the first layer 66 is formed of ePTFE, it
should be understood that in other embodiments the first layer may
comprise other materials. The second layer 67 is preferably formed
of an elastomeric material, including polyurethane elastomers,
silicone rubbers, styrene-butadiene-styrene block copolymers,
polyamide block copolymers, and the like. In a preferred
embodiment, layer 67 is an inner layer relative to layer 66,
although in other embodiments it may be an outer layer. Layer 67
formed of an elastomeric material limits or prevents leakage of
inflation fluid through the microporous ePTFE to allow for
inflation of the balloon 58, and expands elastically to facilitate
deflation of the balloon 58 to a low profile deflated
configuration. The elastomeric material forming layer 67 may
consist of a separate layer which neither fills the pores nor
disturbs the node and fibril structure of the ePTFE layer 66, or it
may at least partially fill the pores of the ePTFE layer 66.
[0033] In the embodiment in which the porous polymeric tube is
formed of ePTFE, the tube 10 is preferably heated at a temperature
sufficient to sinter the ePTFE in a stretched configuration and
again in the compacted configuration, prior to being removed from
mandrel 12. The sintering temperature is typically greater than the
elevated temperature used to heat shrink the heat shrink tube 14 or
wrapped sheet 24 thereon, so that the tube 10 is not sintered
during the heat shrinking of the heat shrink material thereon. In
one embodiment, to provide the desired properties such as the
desired dimension, and dimensional stability (i.e., to minimize
changes in length occurring during inflation of the tubular medical
device or component formed by the compacted porous polymeric tube
(e.g., the compacted ePTFE tube), the porous polymeric tube 10 is
stretched, sintered, compacted according to a method of the
invention, and then sintered again.
[0034] The dimensions of catheter 50 are determined largely by the
size of the balloon and guidewires to be employed, catheter type,
and the size of the artery or other body lumen through which the
catheter must pass or the size of the stent being delivered.
Typically, the outer tubular member 53 has an outer diameter of
about 0.025 to about 0.04 inch (0.064 to 0.10 cm), more
specifically about 0.037 inch (0.094 cm), and a wall thickness of
about 0.002 to about 0.008 inch (0.0051 to 0.02 cm), more
specifically about 0.003 to about 0.005 inch (0.0076 to 0.013 cm).
The inner tubular member 54 typically has an inner diameter of
about 0.01 to about 0.018 inch (0.025 to 0.046 cm), more
specifically about 0.015 to about 0.016 inch (0.038 to 0.04 cm),
and a wall thickness of 0.002 to 0.005 inch (0.005 to 0.013 cm).
The overall working length of the catheter 50 may range from about
100 to about 150 cm, and is typically about 143 cm. The balloon 58
typically has a length of about 0.5 cm to about 6 cm, and an
inflated working diameter of about 2 to about 10 mm.
[0035] Although the shaft is illustrated as having an inner and
outer tubular member, a variety of suitable shaft configurations
may be used including a dual lumen extruded shaft having a
side-by-side lumens extruded therein. Similarly, although the
embodiment illustrated in FIG. 6 is an over-the-wire stent delivery
catheter, the catheter may comprise other types of intravascular
catheters, such as a rapid exchange balloon catheter. Rapid
exchange catheters generally comprise a distal guidewire port in a
distal end of the catheter, a proximal guidewire port in a distal
shaft section and typically spaced a substantial distance from the
proximal end of the catheter, and a short guidewire lumen extending
between the proximal and distal guidewire ports in the distal
section of the catheter.
[0036] While the present invention is described herein in terms of
certain preferred embodiments, those skilled in the art will
recognize that various modifications and improvements may be made
to the invention without departing from the scope thereof.
Moreover, although individual features of one embodiment of the
invention may be discussed herein or shown in the drawings of the
one embodiment and not in other embodiments, it should be apparent
that individual features of one embodiment may be combined with one
or more features of another embodiment or features from a plurality
of embodiments.
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