U.S. patent application number 11/680027 was filed with the patent office on 2007-06-21 for catheter balloon.
This patent application is currently assigned to ADVANCED CARDIOVASCULAR SYSTEMS, INC.. Invention is credited to Srinivasan Sridharan.
Application Number | 20070138694 11/680027 |
Document ID | / |
Family ID | 37886020 |
Filed Date | 2007-06-21 |
United States Patent
Application |
20070138694 |
Kind Code |
A1 |
Sridharan; Srinivasan |
June 21, 2007 |
CATHETER BALLOON
Abstract
An expandable medical device or component thereof including a
tubular body formed of a wrapped sheet of porous polymeric material
fused together, the tubular body having a fused seam at an angle
relative to the longitudinal axis of the tubular body which changes
along the length of the tubular body from a first angle to a second
angle greater than the first angle. The sheet of porous polymeric
material is wound and then fused together such that the winding
angle is less in a first longitudinal section of the tubular body
compared with the winding angle in a second longitudinal section of
the tubular body, in order to provide the second section with
greater resistance to expansion (i.e., lower compliance) than the
first section.
Inventors: |
Sridharan; Srinivasan;
(Morgan Hill, CA) |
Correspondence
Address: |
FULWIDER PATTON LLP
HOWARD HUGHES CENTER
6060 CENTER DRIVE, TENTH FLOOR
LOS ANGELES
CA
90045
US
|
Assignee: |
ADVANCED CARDIOVASCULAR SYSTEMS,
INC.
Santa Clara
CA
|
Family ID: |
37886020 |
Appl. No.: |
11/680027 |
Filed: |
February 28, 2007 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
10331858 |
Dec 30, 2002 |
7195638 |
|
|
11680027 |
Feb 28, 2007 |
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Current U.S.
Class: |
264/248 |
Current CPC
Class: |
A61M 25/104 20130101;
A61M 2025/1075 20130101 |
Class at
Publication: |
264/248 |
International
Class: |
B29C 65/00 20060101
B29C065/00 |
Claims
1-23. (canceled)
24. A method of making an expandable medical device or component
thereof having a tubular body, comprising: a) wrapping a sheet of
porous polymeric material to form a tube having a seam of adjacent
edges, a longitudinal axis, a first longitudinal section with the
seam at a first angle relative to the longitudinal axis of the
tubular body, and a second longitudinal section with the seam at a
second angle greater than the first angle relative to the
longitudinal axis of the tubular body; and b) heating the tube, to
fuse the edges together to form a tubular body having a fused
seam.
25. The method of claim 24 wherein the width of the sheet of porous
polymeric material varies along the length of the sheet, and
wrapping the sheet comprises spirally wrapping the sheet on a
substantially uniform diameter mandrel.
26. The method of claim 24 wherein the width of the sheet of porous
polymeric material is substantially uniform along the length of the
sheet, and wrapping the sheet comprises spirally wrapping the sheet
on a uniform diameter mandrel so that the edges of the sheet have a
smaller amount of overlap in the first section than at a transition
between the first section and the second section.
27. The method of claim 24 wherein the seam is formed by edges of
the sheet which abut oneanother, and wrapping the sheet includes
overlapping portions of the sheet in at least a transition between
the first section and the second section.
28. The method of claim 24 wherein the medical device component is
a catheter balloon and including, after forming the fused seam,
longitudinally stretching the tubular body and thereby increasing
the angle of the seam of the first and second sections.
29. The method of claim 24 wherein a) comprises wrapping the sheet
so that the first angle is about 60 to about 75 degrees.
30. The method of claim 29 wherein a) comprises wrapping the sheet
so that the second angle is about 70 to about 89 degrees.
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 thereof is 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 and the wall expanded 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 to 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 a balloon angioplasty
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 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.
Similarly, vascular grafts comprising cylindrical tubes made from
tissue or synthetic materials such as polyester, expanded
polytetrafluoroethylene, and DACRON may be implanted in vessels to
strengthen or repair the vessel, or used in an anastomosis
procedure to connect vessels 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 are instead expanded 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), which are inflated within the patient's body lumen without
blow molding the ePTFE tubing, have been disclosed. Prior methods
of forming the ePTFE balloon involved wrapping a sheet of ePTFE on
a mandrel and then heating the wrapped sheet to fuse the layers of
wrapped material together. One difficulty has been the failure of
the bond between the ePTFE balloon and the catheter shaft at
relatively low inflation pressures.
[0006] It would be a significant advance to provide a catheter
balloon with improved performance characteristics and ease of
manufacture.
SUMMARY OF THE INVENTION
[0007] This invention is directed to an expandable medical device
or component thereof with a tubular body formed of a wrapped sheet
of porous polymeric material fused together, the tubular body
having a fused seam at an angle relative to the longitudinal axis
of the tubular body, and the angle of the fused seam changes along
the length of the tubular body from a first angle to a second angle
greater than the first angle. The sheet of porous polymeric
material is wound and then fused together such that the winding
angle in a first longitudinal section of the tubular body is less
than the winding angle in a second longitudinal section of the
tubular body, in order to provide the second section with greater
resistance to expansion (i.e., lower compliance) than the first
section.
[0008] In a presently preferred embodiment, the tubular body has a
centrally located section with the fused seam at the first angle.
In one embodiment, the tubular body has a distal section with the
fused seam at the second angle greater than the first angle (i.e.,
the second angle is more nearly perpendicular relative to the
longitudinal axis of the tubular body than is the first angle).
Typically, a proximal section of the tubular body has the fused
seam at a third angle greater than the first angle. The second and
third angles are preferably about equal, although in alternative
embodiments the third angle can be less than or greater than the
second angle. In one embodiment, the angle of the fused seam
changes from the first angle to an intermediate angle between the
first and second angles, to provide multiple changes in the
resistance to expansion along the length of the tubular body.
Similarly, in one embodiment, the angle of the fused seam changes
from the first angle to an intermediate angle between the first and
third angles.
[0009] In a presently preferred embodiment, the expandable medical
device is an inflatable balloon for a catheter. The balloon 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 is an
inflatable member such as a balloon for a catheter, it should be
understood that other expandable medical devices are included
within the scope of the invention, including stent covers and
vascular grafts. The catheter balloon typically has a proximal
skirt section and a distal skirt section bonded to the catheter
shaft so that the interior of the balloon is in fluid communication
with an inflation lumen in the shaft. The balloon has an inflatable
working section between the skirt sections which expands during
inflation of the balloon to perform a procedure such as dilating a
stenosis or implanting a stent, and has inflated sections on either
end of the inflated central working section tapering towards the
skirt sections.
[0010] In a presently preferred embodiment, the fused seam at the
first angle extends along at least a portion of the balloon working
section, and the fused seam at the second angle extends along at
least a portion of one of the proximal or distal skirt sections.
For example, in one embodiment, at least a portion of the distal
skirt section has the fused seam at the second angle greater than
the first angle, and at least a portion of the proximal skirt
section has the fused seam at the third angle greater than the
first angle. Thus, the skirt sections, with the fused seam of the
porous polymeric material at the second angle greater than the
first angle relative to the longitudinal axis of the balloon, have
a greater resistance to expansion than the working length during
inflation of the balloon. As a result, the burst pressure of the
balloon is increased because the bond strength of the skirt
sections is increased. The higher wrap angle of the skirt sections
is believed to provide increased resistance to radial expansion by
inhibiting the tendency of the angle of fused seam to increase due
to rotation of the wrapped porous polymeric sheet during inflation
of the balloon. In one embodiment, the balloon has a burst pressure
(bond seal strength) of about 200 to about 350 psi, preferably
about 250 to about 350 psi In addition to an improved, increased
burst pressure, the increased bond strength in a preferred
embodiment provides increased fatigue resistance so that the
balloon can be inflated multiple times without the bond between the
balloon and shaft failing.
[0011] The proximal and distal inflatable sections (commonly
referred to as the tapered or cone sections of the inflated
balloon), located between the skirt sections and the central
working section, may have the fused seam at the first angle, the
second and third angles, or an intermediate angle between the first
angle and the second and third angles along all or a portion of the
lengths thereof. For example, in one embodiment, a first portion of
the inflatable distal section has the fused seam with the second
angle, and a second portion of the inflatable distal section has
the fused seam with an intermediate angle between the first angle
and the second angle. Consequently, the proximal and distal
inflatable sections which are located at either end of the working
length and which inflate to a tapered configuration are provided
with more resistance to expansion than the working length, and
expand to a smaller diameter than the working length, to further
increase to burst pressure of the balloon.
[0012] In a presently preferred embodiment, the wrapped sheet of
porous polymeric material comprises a polymer selected from the
group consisting of expanded polytetrafluoroethylene (ePTFE), an
ultra high molecular weight polyolefin such as ultra high molecular
weight polyethylene, porous polyethylene, porous polypropylene,
porous polyurethane, and porous nylon. In one embodiment, the
porous material has a node and fibril microstructure. For example,
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 material using conventional methods. In the
embodiment in which the polymeric material of the balloon has a
node and fibril microstructure, after the fused seam is formed, the
tubular body of porous polymeric material is typically further
processed, as for example by being stretched, heated, compacted,
and heated a final time, to form the balloon. However, a variety of
suitable 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
polymeric material cannot be formed into a balloon by conventional
balloon blow molding, and is formed into a balloon by bonding
wrapped layers of the polymeric material together to form a tubular
member, and preferably provided with a nonporous second layer or
liner, to form an inflatable balloon.
[0013] In a method of making an expandable medical device or
component thereof which embodies features of the invention, a sheet
of porous polymeric material is wrapped, typically on a mandrel, to
form a tube having a seam formed by adjacent edges of the sheet, a
longitudinal axis, a first longitudinal section with the seam at a
first angle relative to the longitudinal axis of the tubular body,
and a second longitudinal section with the seam at a second angle
greater than the first angle relative to the longitudinal axis of
the tubular body. The tube is heated, as for example in an oven, to
fuse the longitudinal edges of the wrapped sheet together, to form
a tubular body having a fused seam.
[0014] The wrap angle is dependent upon the inner diameter of the
resulting tubular body (i.e., the outer diameter of the mandrel on
which the sheet is wrapped), and the width of the sheet of porous
polymeric material, and the amount of overlap (if any) between the
longitudinally adjacent wrapped portions of the sheet. In a
presently preferred embodiment, the width of the sheet of porous
polymeric material is substantially uniform along the length of the
sheet. The substantially uniform width of the sheet may vary within
the tolerances used for forming the sheet, and thus the width may
vary typically by about .+-.5% along the length of the sheet. In
order to change the wrap angle at a transition between the sections
having different wrap angles the sheet of porous polymeric material
is typically stretched and/or the amount by which the edge of the
wrapped sheet overlaps the edge of the longitudinally adjacent
portion of wrapped material is changed as the sheet is wrapped
around the mandrel. However, a variety of methods may be used to
increase the wrap angle, such as for example using a sheet having a
varying width (i.e., a greater width in the portion of the length
of the sheet forming the second section of the tubular body), or by
wrapping the sheet on a varying diameter mandrel. In one
embodiment, the sheet is wrapped such that the adjacent edges abut
one another at least along the first section (i.e., the section
having the fused seam at the first angle). However, in alternative
embodiments, the sheet is to wrapped such that the adjacent edges
of the wrapped sheet along the first section are in an overlapping
configuration, although typically with a lesser amount of overlap
than in the remaining sections with the fused seam at a higher
angle.
[0015] The sheet of polymeric material is wrapped along the length
of the mandrel, and is typically wrapped multiple times back over
the underlying length or layer in the opposite direction, to form
multiple layers of the porous material which typically fuse
together during formation of the fused seam. Thus, the tubular body
typically comprises multiple layers of the wrapped sheet, with
adjacent layers of the wrapped sheet having the fused seam at the
given angle of the longitudinal section but oriented in opposite
directions. In one embodiment, during formation of the porous
polymeric tubular body, the sheet of porous polymeric material is
wrapped so that the first angle of the wrapped seam along a first
longitudinal section is about 60 to about 75 degrees, preferably
about 60 to about 70 degrees, and the second angle along a second
longitudinal section is greater than the first angle and is about
70 to about 89 degrees, preferably about 75 to about 85 degrees.
The wrapped sheet is then heated to fuse the wrapped seam and form
the porous polymeric tubular body. However, in the embodiment in
which the device component is a balloon, the resulting porous
polymeric tubular body is typically stretched and/or compacted, or
otherwise further processed, so that the angle of the fused seam
may be increased or decreased along at least a portion of the
length of the tubular body. The wrap angle decreases, and typically
by about 30 to about 90 percent, more specifically about 70 to
about 80 percent, as a result the porous polymeric tube being
longitudinally stretched after formation of the fused seam. For
example, in one embodiment, the wrap angle along the first section
(i.e., the first angle) is originally about 60 to about 70 degrees
after formation of the fused seam, and thereafter is caused to
decrease to about 15 to about 25 degrees as a result of the porous
polymeric tube being longitudinally stretched. In one embodiment,
the porous polymeric tube is longitudinally compacted, typically
after being longitudinally stretched, causing the wrap angle to
increase as a result of the longitudinal compaction. Although the
absolute value of the wrap angle of the fused seam may change as a
result of such subsequent processing following the wrapping and
fusing which forms the fused seam, the wrap angle of the fused seam
in the finished balloon will remain greater in the second section
than in the first section. For example, in one embodiment, first
angle of the fused seam of the finished balloon (after any
stretching or compacting processing) is about 10% to about 80% of
the second angle and preferably 10% to about 50% of the second
angle. In one embodiment, the fused seam of the finished balloon
has a first angle of about 15 to about 75 degrees and preferably
about 15 degrees to about 35 degrees, and a second angle (greater
than the first angle) of about 25 to about 89 degrees and
preferably about 50 degrees to about 89 degrees.
[0016] The expandable medical device or component thereof is
provided with variable resistance to expansion along the length
thereof due to the varying wrap angle of the porous polymeric
sheet. In the embodiment in which the porous polymeric sheet forms
a layer of a catheter balloon having at least one layer, the
strength of the bond between the balloon and the catheter shaft is
increased. Moreover, the working length of the balloon and tapered
sections inflate to more clearly delineated sections due to the
varying wrap angle, with the well defined working length
facilitating stent positioning in the embodiment in which the
balloon catheter is used for stent delivery. 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
[0017] FIG. 1A is an elevational view, partially in section, of a
stent delivery balloon catheter embodying features of the
invention.
[0018] FIG. 1B illustrates the balloon of FIG. 1A fully
inflated.
[0019] FIGS. 2 and 3 are transverse cross sectional views of the
balloon catheter shown in FIG. 1, taken along lines 2-2, and 3-3,
respectively.
[0020] FIG. 4 is an elevational view of an assembly of a sheet of
porous polymeric material wrapped on a mandrel to form a tube
during formation of a layer of the balloon of FIG. 1, in which the
sheet has a seam with a first angle at a central section of the
tube and a second angle at end sections of the tube.
[0021] FIG. 5 illustrates the assembly shown in FIG. 4, partially
in longitudinal cross section.
[0022] FIG. 6 is a transverse cross sectional view of the assembly
shown in FIG. 5, taken along line 6-6.
[0023] FIG. 7 is an elevational view of an assembly of a sheet of
porous polymeric material wrapped on a mandrel during formation of
a layer of the balloon of FIG. 1 in an alternative embodiment in
which the sheet has a seam with an intermediate angle between the
first angle of the central section and the second angle of the end
sections.
DETAILED DESCRIPTION OF THE INVENTION
[0024] FIG. 1A illustrates an over-the-wire type stent delivery
balloon catheter 10 embodying features of the invention. Catheter
10 generally comprises an elongated catheter shaft 12 having an
outer tubular member 14 and an inner tubular member 16. Inner
tubular member 16 defines a guidewire lumen 18 configured to
slidingly receive a guidewire 20, and the coaxial relationship
between outer tubular member 14 and inner tubular member 16 defines
annular inflation lumen 22, as best shown in FIG. 2 illustrating a
transverse cross section view of the distal end of the catheter
shown in FIG. 1A, taken along line 2-2. An inflatable balloon 24
disposed on a distal section of catheter shaft 12 has a proximal
skirt section 25 sealingly secured to the distal end of outer
tubular member 14 and a distal skirt section 26 sealingly secured
to the distal end of inner tubular member 16, so that its interior
is in fluid communication with inflation lumen 22. An adapter 30 at
the proximal end of catheter shaft 12 is configured to provide
access to guidewire lumen 18, and to direct inflation fluid through
arm 31 into inflation lumen 22. In the embodiment illustrated in
FIG. 1A, the balloon 24 is shown prior to being fully inflated in a
patient's body lumen 27, and with an expandable stent 32 having
expandable tubular stent cover 35 mounted thereon. The distal end
of the catheter may be advanced to a desired region of a patient's
body lumen 27 in a conventional manner and balloon 24 may be
inflated to expand covered stent 32, seating the covered stent 32
in the body lumen 27. FIG. 1B illustrates the balloon catheter 10
of FIG. 1A, with the balloon 24 fully inflated to expand the
covered stent 32 within the body lumen 27. Inflated balloon 24 has
a centrally located working length with stent 32 thereon, and
proximal and distal inflatable sections (i.e., inflated tapered
sections) at either end of the working length between the working
length and the respective skirt section 25, 26 of the balloon
[0025] In the embodiment illustrated in FIG. 1, balloon 24 has a
first layer 33 and a second layer 34. In a presently preferred
embodiment, the balloon 24 has at least one layer comprising a
porous polymeric material, and preferably a microporous polymeric
material having a node and fibril microstructure, such as ePTFE. In
the embodiment illustrated in FIG. 1, first layer 33 is formed of
ePTFE, and the second layer 34 is formed of a polymeric material
preferably different from the polymeric material of the first layer
33. Although discussed below in terms of one embodiment in which
the first layer 33 is formed of ePTFE, it should be understood that
the first layer may comprise other materials including ultrahigh
molecular weight polyethylene. The second layer 34 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 34 forms an inner layer of balloon 24,
although in other embodiments it may be on the exterior of the
layer 33. Layer 34 limits or prevents leakage of inflation fluid
through the microporous ePTFE layer 33 to allow for inflation of
the balloon 24, and expands elastically to facilitate deflation of
the balloon 24 to a low profile deflated configuration. The layer
34 may consist of a separate layer which neither fills the pores
nor disturbs the node and fibril structure of the ePTFE layer 33,
or it may at least partially fill the pores of the ePTFE layer
33.
[0026] The ePTFE layer 33 is formed according to a method which
embodies features of the invention, in which a sheet of ePTFE is
wrapped to form a tube, and then heated to fuse the wrapped
material together. In accordance with a method of the invention,
the sheet is wrapped such that the wrap angle varies along the
length of the tube.
[0027] FIG. 4 illustrates an assembly of a sheet 40 of porous
polymeric material (e.g., ePTFE) wrapped around a mandrel 41 and
fused to form a porous polymeric tube, during the formation of the
ePTFE layer 33 of the balloon 24 of FIG. 1. In the embodiment of
FIG. 4, the tube has a centrally located section 44 with the fused
seam 43 at a first angle of about 63 to about 65 degrees relative
to the longitudinal axis of the tube, and a first end section 45
with the fused seam 43 at a second angle of about 76 to about 78
degrees, and a second end section 46 with the fused seam 43 a third
angle about equal to the second angle. Although illustrated at
about 76 degrees in FIG. 4, it should be understood that in a
presently preferred embodiment the second angle is preferably as
close to 90 degrees as possible while allowing the sheet 40 to
progress helically along the length of the mandrel 41.
Additionally, although the fused seam 43 is illustrated in FIG. 4
as highly visible lines along the tube for ease of illustration, it
should be understood that the fused seam 43 in the finished balloon
is generally not highly visible to the naked eye. FIG. 5
illustrates a longitudinal cross sectional view of the assembly of
FIG. 4, and FIG. 6 illustrates a transverse cross sectional view of
the assembly of FIG. 5, taken along lines 6-6.
[0028] Preferably the centrally located section 44 of the tube of
FIG. 4 corresponds to the inflatable sections of the balloon 24 of
FIG. 1 (i.e., the inflatable working length with the stent 32
mounted thereon, and the inflated proximal and distal tapered
sections on either end of the working length). The first and second
end sections 45, 46 correspond to the proximal and distal skirt
sections 25, 26 of balloon 24 of FIG. 1, which are secured to the
catheter shaft 12. The angles illustrated in FIG. 4 are the angles
which are present following wrapping and fusing of the sheet prior
to any further processing steps, such as longitudinally stretching
and/or compacting the porous polymeric tube, which may change the
wrap angles. Additionally, inflation of the balloon typically
increases the first wrap angle of the central section of the
balloon as the wrapped sheet unwinds during expansion.
[0029] The sheet 40 of polymeric material is preferably wrapped
along a length of the mandrel 41 to form at least one layer of
wrapped material. In a presently preferred embodiment, multiple
layers of polymeric material are wrapped on the mandrel, by
wrapping the sheet 40 down the length of the mandrel 41 to form a
first layer and then back again over the first layer one or more
times to form additional layers, which in one embodiment results in
three to five layers, preferably about four layers of material
forming the ePTFE layer 33 of balloon 24. Thus, although
illustrated in FIG. 5 as a single layer of wrapped material, it
should be understood that the sheet 40 typically forms multiple
layers on the mandrel 41. The multiple layers of ePTFE are
typically fused together to produce the tube forming layer 33 of
balloon 24. Because the adjacent layers of the sheet are wrapped in
opposite directions along the length of the mandrel, the adjacent
layers have the fused seam oriented in opposite directions.
However, the respective angles of the fused seam (i.e, first,
second or third angles) of the various longitudinal sections of the
tube remain the same in the adjacent layers, although in opposite
directions.
[0030] In the embodiment of FIG. 1, the sheet 40 is a long strip of
polymeric material having longitudinal edges along the length of
the strip which are longer than the width of the sheet 40. The
sheet 40 is wrapped on the mandrel 41 so that the longitudinal
edges of the sheet 40 are brought together in an abutting or
overlapping relation, and the fused seam 43 joins the abutting or
overlapping edges together. In a presently preferred embodiment,
the fused seam 43 is formed by edges of the wrapped sheet 40 which
abut oneanother, at least along the centrally located section
44.
[0031] In order to transition from the first angle to the
second/third angle during wrapping of the sheet 40 from one end to
the other end of the mandrel 41, the sheet 40 is typically
stretched and/or caused to overlap a portion of the preceding turn
of the sheet 40 in a transition section. In the embodiment
illustrated in FIG. 5, portions of the preceding turns of the
sheets are covered by the adjacent turn of the sheet in the
transition sections and in the first and second end sections 45,
46, in order to form the first and second angles. Although FIG. 5
illustrates an embodiment in which the edges of the sheet 40
overlap oneanother along the first and second end sections 45, 46,
to form the seam having a larger angle than the seam along the
central section 44, it should be understood that in alternative
embodiments the edges of the sheet abut oneanother along the first
and second end sections 45, 46, as for example by the sheet 40
being stretched (to change the width of the sheet) during winding
of the first and second end sections 45, 46. In the embodiment of
FIG. 5, the width of the sheet 40 and the outer diameter of the
mandrel 41 are such that the sheet 40 can be wrapped with abutting
edges forming the seam at an angle of about 65 degrees in the
central section 44.
[0032] In the embodiment of FIGS. 4 and 5, the fused seam angle
transitions directly from the first to the second angle. However,
in alternative embodiments, an intermediate longitudinal section is
provided between the section with the fused seam at the first angle
and the other sections of the tube, the intermediate section having
an intermediate angle greater than the first angle and less than
the second/third angles. The intermediate angle provides a section
having greater resistance to expansion than the section with the
fused seam at the first angle, and less resistance to expansion
than the sections with the second/third angles. FIG. 7 illustrates
an assembly of a wrapped sheet 40 of porous polymeric material on
mandrel 41, with proximal and distal intermediate sections 47, 48
having the fused seam at an intermediate angle between the first
and second/third angles. In the embodiment of FIG. 7, the
intermediate angle is about 70 degrees, although a variety of
suitable intermediate angles may be used. In one embodiment, the
sheet 40 of porous polymeric material is wrapped so that the
intermediate angle, prior to any stretching or compacting of the
porous polymeric tube, is about 65 to about 85 degrees, more
particularly about 68 to about 75 degrees. The intermediate angle
in the finished balloon (after any stretching and/or compacting of
the porous polymeric tube) is typically about 85% to about 95% of
the second angle, and more specifically is typically about 20 to
about 85 degrees. The intermediate sections 47, 48 correspond at
least in part to the inflatable proximal and distal sections (i.e.,
inflated tapered sections) at either end of the working length of
the balloon 24 in FIG. 1B. Although illustrated in FIG. 7 with the
fused seam angle varying from about 78 degrees at the end sections
45, 46, to about 70 degrees at the intermediate sections 47, 48,
and further to about 63 degrees at the central section 44, it
should be understood that a tube with a variable fused seam angle
in accordance with the invention may have a variety of sections
with a variety of angles. The transitions between the intermediate
sections 47, 48 and the adjacent longitudinal sections are formed
as discussed above in relation to the embodiment of FIG. 5.
[0033] The sheet 40 is preferably a polymeric material having a
microporous structure, which in one embodiment has a node and
fibril structure, such as ePTFE. The sheet 40 preferably has the
desired microstructure (e.g., porous and/or node and fibril) before
being wrapped on the mandrel 41. In a presently preferred
embodiment, the sheet 40 of ePTFE is partially-sintered before
wrapping.
[0034] After the fused seam 43 is formed, the tubular body is
typically further processed prior to being bonded to the layer 34
to form the balloon 24. Preferably, the tubular body is further
processed by being stretched, sintered, compacted, and then
sintered again, to provide the desired properties such as the
desired dimension, and dimensional stability (e.g., to minimize
changes in length occurring during inflation of the balloon). For
example, in one embodiment, the tubular body is longitudinally
stretched to thereby increase the length of the tubular body by
about 50% to about 200%. After the longitudinal stretching, the
tubular body is preferably compacted and heated to further sinter
the material, to provide the desired performance characteristics
for balloon 24. The tubular body is typically heated in an oven at
about 360.degree. C. to about 380.degree. C., or to at least the
melting point of the ePTFE. The stretching and/or compaction
typically affects the angle of the fused seam. In one embodiment,
the finished balloon layer 33 (prior to inflation of the balloon),
produced from the tube of FIG. 7 having the fused seam at the
angles shown in FIG. 7, has the fused seam at angles along at least
some of the sections 44, 45, 46, 47, 48 which are less than the
angles shown in FIG. 7 as a result of the further processing. The
completed ePTFE layer 33 is then bonded to or otherwise combined
with the elastomeric liner 34 to complete the balloon 24 with the
balloon 24 secured to the catheter shaft 12.
[0035] The dimensions of catheter 10 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 14 has an outer diameter of
about 0.025 to about 0.04 inches (0.064 to 0.10 cm), usually about
0.037 inches (0.094 cm), the wall thickness of the outer tubular
member 14 can vary from about 0.002 to about 0.008 inches (0.0051
to 0.02 cm), typically about 0.003 to 0.005 inches (0.0076 to 0.013
cm). The inner tubular member 16 typically has an inner diameter of
about 0.01 to about 0.018 inches (0.025 to 0.046 cm), usually about
0.016 inches (0.04 cm), and wall thickness of 0.004 to 0.008 inches
(0.01 to 0.02 cm). The overall length of the catheter 10 may range
from about 100 to about 150 cm, and is typically about 143 cm.
Balloon 24 typically has a length of about 5 to about 60 mm, and an
inflated working diameter of about 2 to about 10 mm. In one
embodiment, the skirt sections 25, 26 of the balloon 24 typically
have a length of about 0.5 to about 7 mm, and the central working
section of the balloon 24 has a length greater than the skirt
sections and equal to about 5 to about 40 mm.
[0036] Inner tubular member 16 and outer tubular member 14 can be
formed by conventional techniques, for example by extruding and
necking materials already found useful in intravascular catheters
such a polyethylene, polyvinyl chloride, polyesters, polyamides,
polyimides, polyurethanes, and composite materials. The various
components may be joined using conventional bonding methods such as
by fusion bonding or use of adhesives. 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
shaft having a side-by-side lumens therein. Similarly, although the
embodiment illustrated in FIG. 1 is an over-the-wire stent delivery
catheter, balloons of this invention may also be used with other
types of intravascular catheters, such as rapid exchange dilatation
catheters. 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 distal of the proximal end
of the shaft 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.
[0037] 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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