CA2243277A1 - Lubricous and readily bondable catheter shaft - Google Patents
Lubricous and readily bondable catheter shaft Download PDFInfo
- Publication number
- CA2243277A1 CA2243277A1 CA002243277A CA2243277A CA2243277A1 CA 2243277 A1 CA2243277 A1 CA 2243277A1 CA 002243277 A CA002243277 A CA 002243277A CA 2243277 A CA2243277 A CA 2243277A CA 2243277 A1 CA2243277 A1 CA 2243277A1
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- Canada
- Prior art keywords
- catheter
- polymeric
- lubricious
- balloon
- intraluminal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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Abstract
An intraluminal catheter, particularly a dilatation catheter for angioplasty procedures, which has a shaft section formed of a blend of lubricous and bonding polymeric components in proportions to maintain a low coefficient of friction while maintaining the ability to bond non-lubricous polymeric material, e.g. polyethylene terephthalate, to the segment.
Description
CA 02243277 1998-07-1~
W 097/26027 PCTrUS97/00843 I I IBRICOUS AND RF~DILY BONI:)AB! F CATHFTF~ SHAFT
- R''.CKGROUN~ C~F THF INVENTION
This invention relates to catheters for performing intrav~scul~r 5 procedures such as percutaneous transluminal coronary angioplasty (PTCA) and more specificaliy to elongated sha~ts for such catheters.
PTCA is now one of the most widely used treatment modalities for heart disease. The procedure basically comprises advancing a dilatation catheter, having an inflatable balloon on its distal extremity, into the 10 patient's coronary anatomy over a guidewire until the balioon of the dilatation catheter is properly positioned across the lesion to be dilated. Once properly positioned, the dilatation balloon is infiated with liquid to a predetermined size at relatively high pressures, e.g. up to 20 atmospheres or more, to expand the arterial passageway. Generally, the inflated SUE~;TITUTE SI~EET ~F~ULI~ 26) CA 02243277 1998-07-1~
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. After the balloon is finally deflated, blood flow resumes through the dilated artery and the dilatation catheter can be removed therefrom.
In most PTCA procedures, a guiding catheter having a preshaped distal tip is first percutaneously introduced into the cardiovascular system of a patient by means of a conventional Seldinger technique and advanced therein until the preshaped distal tip of the guiding 10 catheter is disposed within the aorta adjacent to the ostium of the desired coronary artery. The guiding catheter is twisted or torqued from its proximal end, which extends out of the patient, to guide the distal tip of the guiding catheter into the desired coronary ostium. Once the guiding catheter is in proper position within the patient's vasculature, the dil~t~tion 1~ catheter with a guidewire slidably disposed within an inner lumen of the dilatation catheter is positioned within the inner lumen of the guiding catheter. The guidewire is first advanced out the distal tip of the guiding catheter seated in the coronary ostium into the patienrs coronary artery and directed to the region of the patient's coronary anatomy where the 20 procedure is to occur. A torque may be applied to the proximal end of the SUBSTITUTE SHEET (F~ULE 26~
-CA 02243277 1998-07-1~
W O 97/26027 PCT~US97100843 guidewire, which extends out of the proximal end of the guiding catheter, to guide the curved or otherwise shaped distal end of the guidewire into a desired branch of the coronary artery. The advancement of the guidewire within the selected artery continues until it crosses the lesion to be dilated.
5 The dilatation catheter is then advanced over the previously advanced guidewire, until the balloon on the distal extremity of the dilatation catheter is properly positioned across the lesion which is to be dilated.
Current intravascular catheter designs are limited by the need to incorporate conflicting characteristics. For example, most dilatation catheters 10 are designed to be introduced into a body lumen over an in-place guidewire which is slidably received within an inner lumen within the catheter. As such, it is desirable to ",i"i"li~e the friction between the guidewire and the surface of the inner lumen of the catheter by constructing the catheter from a lubricous material such as a high density 15 polyethylene. However, lubricous polymeric materials frequently lack other desirable properties, including, for example, the ability to readily bond to incompatible polymeric materials such as polyethylene terephthalate and nylon. Due to the high inflation pressures (up to 300 psi or more) associated with coronary balloon angioplasty, it is imperative to provide a 20 ~trorg bor;d be.~v~veer, or;e or more erd~ of the dilatatior. balloor, ar.d the SUB5T~Tl)~E S~IEET ~P~IJLE 26~
CA 02243277 1998-07-1~
catheter shaft. Polyolefin balloons can be effectively fusion bonded to a polyethylene shaft but ballo~5ns made of nylon and other polyamide materials, and balloons made of polyesters such as polyethylene terephthalate do not easily bond to polyolefinic materials. Nylon and 5 polyethylene terephthalate balloons usually require surface treatment and the use of a suitable adhesive to bond to polyolefin materials such as polyethylene. The additional manufacturing steps of surface treatments and incorporating and curing an adhesives, greatly complicate the manufacturing process and can introduce significant quality control problems. A catheter 10 shaft should also have adequate strength for pushability and resistance to buckling or kinking. As another example, it may be desirable to provide a catheter shaft with elastomeric properties to improve flexibility. However, most lubricous materials are not elastomeric.
United States Patent No. 5,304,134 to Kraus et al., which is 15 hereby incorporated in its entirety by reference, attempts to provide a solution to the poor bonding of lubricous by providin~ the catheter shaft with an inner tubular member havlng a lubricous proximat portion and a non-lubricous, bondable distal portion. However, this approach does not represent a complete solution, because the lubricous proximal portion must 20 still be bonded to the non-lubricous distal portion. The Kraus et al. system SUB~;TITI~TE SHEET ~RULE 26~
CA 02243277 1998-07-1~
W O 97/26~27 PCTrUS97/00843 also requires that some portion of the guidewire lumen be formed from a non- lubricous material which restricts guidewire movement within the lumen.
A different approach involves forming the dilatation balloon as 5 an integral portion of the catheter shaft itself, but this requires the balloon and the shaft to be formed from the same material, which is not always desirable because the property requirements for the balloon and the shaft can be quite different, particularly for dilatation catheters for PTCA .
Accordingly, there remains a need to provide a catheter shaft 10 having a lubricous inner surface defining a guidewire lumen while allowing an easy, secure bond with a dilatation balloon or other catheter components formed of non-lubricous polymeric materials. The present invention s-dli~r,es these and other needs.
SUMMARY C)F THF INVFlaTION
The present invention is directed to an intravascular catheter, such as a balloon dilatation catheter for performing angioplasty procedures, which has a shaft or shaft segment which is both lubricous and is capable of readily bonding to other catheter components such as a balloon forrned 20 of essentially non-lubricous polymers.
~UBSTITUT~ S~EET (RULE 26) CA 02243277 1998-07-1~
W 097/26027 PCTrJS97/00843 In accordance with the present invention, the catheter shaft or catheter shaft segment is formed of a polymeric blend comprising at least about 30% by weight, preferably at least about 50% by weight of a lubricous polymeric component, not more than about 60%, preferably not 5 more than about 40% of a bonding polymeric component and up to about 30%, preferably not more than about 10% of a polymeric component for compatiblizing the lubricous and bonding components. Optionally, up to 25%
by weight, usually not more than about 10% by weight of the blend should be a catalytic material to facilitate cross linking the shaft material 10 after forming the product. The lubricous component and the bonding component must be compatible or capable of bein~ made compatible. As used herein the term "compatible" and words of similar import mean that two polymer materials readily form an inli,-,ate mixture when they are melt processed together. Usually, they are miscible when both are in a molten 1 5 condition.
In one presently preferred embodiment, the catheter or catheter segment is formed of a blend of about 50% to about 80%
polyethylene (a lubricous component), about up to about 50% of a copolyester such as Hytrel~) (the bonding component) and up to about 50%
20 of a compatiblizing agent such as an acrylate. The polymer components are SlJBSTITUTE SHFET ~P~ULI~ 26~
- CA 02243277 1998-07-1~
W O 97/26027 PCT~U~,97/00843 i"li",~lely-mixed and extruded into a tubu,ar product which is utilized as the inner tubular member of an intravascular catheter. The surface defining an inner lumen of the tubular member has a kinematic frictional coefficient of about 0.08 to about 0.3 on a smooth glass. A balloon formed of PET
5 readily fusion bonds to the outer surFace of the tubular member.
These and other advantages of the invention will become more apparent from the following detailed description of the invention when taken in conjunction with the accompanying exemplary drawings.
IFF DF-~CRIPTION OF THF DRAWINGS
Fig. 1 is an elevational view, partially in section, of an over-the-wire dilatation catheter having an inner tubular member embodying features of the invention.
Fig. 2 is a transverse cross section of the embodiment shown in Fig. 1 taken along the lines 2-2.
Fig. 3 is an elevational view, partially in section, of the distal section of a rapid exchange type dilatation catheter having an inner tubular member embodying features of the invention.
SUBST~TlJTE SHEET (R.,ILE ~6 CA 02243277 1998-07-1~
W 097/26027 PCT~US97/00843 - Fig. 4 is a transverse cross section of the embodiment shown in Fig. 4 taken along the line~ 5-5.
Fig. 5 is an elevational view, partially in section, of an alternative embodiment wherein the distai section of the catheter shaft is formed of an 5 extrusion of a polymerblend.
Fig. 6 is a transverse cross section of the embodiment shown in Fig. 6 taken along the lines 7-7.
nFTAI5 Fn DESCRIPTION OF THF INVFI~ITION
Reference is made to Figs. 1 and 2 which illustrate a balloon dilatation catheter 10 embodying features of the invention. Generally, the call ,eler 10 comprises an outer tubular member 1 1, an inner tubular member 12, a dilatation balloon 13 on a distal portion of the caLl,eter and ,an adapter 14 on the proximal end of the catheter. The inner tubular 15 member 12 has a guidewire receiving inner lumen 15 which slidably receives guidewire 16. The outer surface of the inner tubular member 12 and the inner surface of the outer tubular member 11 define an annular inflation lumen 17 which is in fluid communication with the interior of balloon 13 and side arm 18 of adapter 14.
SUBSTITUT~ SHEE~ ~IILE 26) CA 02243277 1998-07-1~
W O 97/26027 PCTrUS97/00843 The distal skirt 20 of balloon 13 is bonded, preferably fusion bonded, to the exterior of th~ inner tubular member 12 and the proximal skirt 21 is fusion bonded to the exterior of the outer tubular member 11.
The fusion bonds are preferably formed by applying laser energy to the 5 exterior of the skirts 20 and 21 which ca-lses the interface between the skirts and the exterior of the outer and inner tubular members 12 and 13.
In one presently preferred embodiment, both the outer and inner tubular members 11 and 12 are formed of a polymer blend in accordance with the invention.
Figs. 34 depict another embodiment of the invention directed to a rapid exchange type dilatation catheter 30. The catheter 30 includes a relatively stiff proximal shaft 31 formed of hypotubing and a relatively flexible distal shaft section 32. The distal shaft section 32 includes an inner tubular member 33, an outer tubular member 34 and a dilation balloon 35.
15 The inner tubular member 33 has a guidewire receiving inner lumen 36 which is in fluid communication with a distal guidewire port 37 in the distal end of the catheter 10 and a proximal guidewire port 38 disposed a short distance, e.g. about 10 to about 45 cm from the proximal end of the balloon 35. The proximal shaft 31 comprises a metallic hypotube 40 (e.g.
20 stainless steel or NiTi alloys) and an outer polymer jacket 41 formed of SUB~ITUTE SHEET ~ E ~6~
CA 02243277 1998-07-1~
suitable poiymer material such as high density polyethylene. The distal end 32 of the hypotube 40 is truncated and fits into the interior of the outer - tubular member 34 and bonded thereto by suitable adhesive 42. Support tube 43, preferably formed of polyimide, is disposed between the inner and outer tubular members 33 and 34 and defines inflation lumen 44. As shown in more detail in Figs. 4 and 5, the outer tubular member is partially bonded to the inner tubular member 33 and partially to the support tube 43.
A filler material 46, such as 75/25 high density/low density polyethylene, is disposed between the outer tubular member 34 and the support tube 43.
In the embodiment of Figs. 3-4 the inner tubular member 33 is rc ~" ,ed of a polymer blend in accordance with the present invention. The distal skirt 47 of balloon 35 is fusion bonded to the exterior of the inner tubular member 33 as in the previously discussed embodiment shown in Figs.1 and 2. The proximal skirt 48 of the balloon 35 forms the outer tubular member 34 and is formed of essentially the same material as the balloon. In an alternative embodiment not shown the outer tubular member 34 may be a member separate and distinct from the balloon and formed of a polymer blend in accordance with the present invention. In this latter case the proximal skirt of the balloon 35 is fusion bonded to the exterior of the outer tubular member.
SUB~TITl iTE SH~ R~JLE ~t3) CA 02243277 1998-07-1~
WO 97/26027 PCTrUS97/00843 - Figs. 5 and 6 illustrate yet another embodiment of the invention wherein the catheter 50 has a distal shaft 51 which is of a dual lumen construction and is formed by extruding a poiymer blend in accordance with the present invention. A tubuiar extension 52 extends 5 through the interior of the dilatation balloon 53 and has a distal guldewire port 54 in its distal end. The balloon 53 has a distal skirt 55 fusion bonded to the distal end of the tubular extension 52 and a proximal skirt 56 fusion bonded to the distal shaft 51 as shown in the drawings.
A presently preferred polymer blend includes about 65% high 10 density polyethylene, about 30% Hytrel(~) (available from Dupont) and about 5% ethylene methyl acrylate such as Lotryl 24MA005 (available from Elf ATOCHEM). This blend readily fusion bonds to polyethylene terephthalate and has a coefficient of friction of about 0.1-0.2.
Although individual features of embodiments of the invention 15 may be shown in some of the drawings and not in others, those skilled in the art will recognize that individual features of one embodiment of the invention can be combined with any or all the features of another embodiment. A variety of modifications can be made to the present invention without departing from the scope thereof.
SUBSTITUTE SHEET ~RU~E 2~3 . ' i~'t~.A; ,~-t=! ! - ~ ~yt~
W 097/26027 PCTrUS97/00843 I I IBRICOUS AND RF~DILY BONI:)AB! F CATHFTF~ SHAFT
- R''.CKGROUN~ C~F THF INVENTION
This invention relates to catheters for performing intrav~scul~r 5 procedures such as percutaneous transluminal coronary angioplasty (PTCA) and more specificaliy to elongated sha~ts for such catheters.
PTCA is now one of the most widely used treatment modalities for heart disease. The procedure basically comprises advancing a dilatation catheter, having an inflatable balloon on its distal extremity, into the 10 patient's coronary anatomy over a guidewire until the balioon of the dilatation catheter is properly positioned across the lesion to be dilated. Once properly positioned, the dilatation balloon is infiated with liquid to a predetermined size at relatively high pressures, e.g. up to 20 atmospheres or more, to expand the arterial passageway. Generally, the inflated SUE~;TITUTE SI~EET ~F~ULI~ 26) CA 02243277 1998-07-1~
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. After the balloon is finally deflated, blood flow resumes through the dilated artery and the dilatation catheter can be removed therefrom.
In most PTCA procedures, a guiding catheter having a preshaped distal tip is first percutaneously introduced into the cardiovascular system of a patient by means of a conventional Seldinger technique and advanced therein until the preshaped distal tip of the guiding 10 catheter is disposed within the aorta adjacent to the ostium of the desired coronary artery. The guiding catheter is twisted or torqued from its proximal end, which extends out of the patient, to guide the distal tip of the guiding catheter into the desired coronary ostium. Once the guiding catheter is in proper position within the patient's vasculature, the dil~t~tion 1~ catheter with a guidewire slidably disposed within an inner lumen of the dilatation catheter is positioned within the inner lumen of the guiding catheter. The guidewire is first advanced out the distal tip of the guiding catheter seated in the coronary ostium into the patienrs coronary artery and directed to the region of the patient's coronary anatomy where the 20 procedure is to occur. A torque may be applied to the proximal end of the SUBSTITUTE SHEET (F~ULE 26~
-CA 02243277 1998-07-1~
W O 97/26027 PCT~US97100843 guidewire, which extends out of the proximal end of the guiding catheter, to guide the curved or otherwise shaped distal end of the guidewire into a desired branch of the coronary artery. The advancement of the guidewire within the selected artery continues until it crosses the lesion to be dilated.
5 The dilatation catheter is then advanced over the previously advanced guidewire, until the balloon on the distal extremity of the dilatation catheter is properly positioned across the lesion which is to be dilated.
Current intravascular catheter designs are limited by the need to incorporate conflicting characteristics. For example, most dilatation catheters 10 are designed to be introduced into a body lumen over an in-place guidewire which is slidably received within an inner lumen within the catheter. As such, it is desirable to ",i"i"li~e the friction between the guidewire and the surface of the inner lumen of the catheter by constructing the catheter from a lubricous material such as a high density 15 polyethylene. However, lubricous polymeric materials frequently lack other desirable properties, including, for example, the ability to readily bond to incompatible polymeric materials such as polyethylene terephthalate and nylon. Due to the high inflation pressures (up to 300 psi or more) associated with coronary balloon angioplasty, it is imperative to provide a 20 ~trorg bor;d be.~v~veer, or;e or more erd~ of the dilatatior. balloor, ar.d the SUB5T~Tl)~E S~IEET ~P~IJLE 26~
CA 02243277 1998-07-1~
catheter shaft. Polyolefin balloons can be effectively fusion bonded to a polyethylene shaft but ballo~5ns made of nylon and other polyamide materials, and balloons made of polyesters such as polyethylene terephthalate do not easily bond to polyolefinic materials. Nylon and 5 polyethylene terephthalate balloons usually require surface treatment and the use of a suitable adhesive to bond to polyolefin materials such as polyethylene. The additional manufacturing steps of surface treatments and incorporating and curing an adhesives, greatly complicate the manufacturing process and can introduce significant quality control problems. A catheter 10 shaft should also have adequate strength for pushability and resistance to buckling or kinking. As another example, it may be desirable to provide a catheter shaft with elastomeric properties to improve flexibility. However, most lubricous materials are not elastomeric.
United States Patent No. 5,304,134 to Kraus et al., which is 15 hereby incorporated in its entirety by reference, attempts to provide a solution to the poor bonding of lubricous by providin~ the catheter shaft with an inner tubular member havlng a lubricous proximat portion and a non-lubricous, bondable distal portion. However, this approach does not represent a complete solution, because the lubricous proximal portion must 20 still be bonded to the non-lubricous distal portion. The Kraus et al. system SUB~;TITI~TE SHEET ~RULE 26~
CA 02243277 1998-07-1~
W O 97/26~27 PCTrUS97/00843 also requires that some portion of the guidewire lumen be formed from a non- lubricous material which restricts guidewire movement within the lumen.
A different approach involves forming the dilatation balloon as 5 an integral portion of the catheter shaft itself, but this requires the balloon and the shaft to be formed from the same material, which is not always desirable because the property requirements for the balloon and the shaft can be quite different, particularly for dilatation catheters for PTCA .
Accordingly, there remains a need to provide a catheter shaft 10 having a lubricous inner surface defining a guidewire lumen while allowing an easy, secure bond with a dilatation balloon or other catheter components formed of non-lubricous polymeric materials. The present invention s-dli~r,es these and other needs.
SUMMARY C)F THF INVFlaTION
The present invention is directed to an intravascular catheter, such as a balloon dilatation catheter for performing angioplasty procedures, which has a shaft or shaft segment which is both lubricous and is capable of readily bonding to other catheter components such as a balloon forrned 20 of essentially non-lubricous polymers.
~UBSTITUT~ S~EET (RULE 26) CA 02243277 1998-07-1~
W 097/26027 PCTrJS97/00843 In accordance with the present invention, the catheter shaft or catheter shaft segment is formed of a polymeric blend comprising at least about 30% by weight, preferably at least about 50% by weight of a lubricous polymeric component, not more than about 60%, preferably not 5 more than about 40% of a bonding polymeric component and up to about 30%, preferably not more than about 10% of a polymeric component for compatiblizing the lubricous and bonding components. Optionally, up to 25%
by weight, usually not more than about 10% by weight of the blend should be a catalytic material to facilitate cross linking the shaft material 10 after forming the product. The lubricous component and the bonding component must be compatible or capable of bein~ made compatible. As used herein the term "compatible" and words of similar import mean that two polymer materials readily form an inli,-,ate mixture when they are melt processed together. Usually, they are miscible when both are in a molten 1 5 condition.
In one presently preferred embodiment, the catheter or catheter segment is formed of a blend of about 50% to about 80%
polyethylene (a lubricous component), about up to about 50% of a copolyester such as Hytrel~) (the bonding component) and up to about 50%
20 of a compatiblizing agent such as an acrylate. The polymer components are SlJBSTITUTE SHFET ~P~ULI~ 26~
- CA 02243277 1998-07-1~
W O 97/26027 PCT~U~,97/00843 i"li",~lely-mixed and extruded into a tubu,ar product which is utilized as the inner tubular member of an intravascular catheter. The surface defining an inner lumen of the tubular member has a kinematic frictional coefficient of about 0.08 to about 0.3 on a smooth glass. A balloon formed of PET
5 readily fusion bonds to the outer surFace of the tubular member.
These and other advantages of the invention will become more apparent from the following detailed description of the invention when taken in conjunction with the accompanying exemplary drawings.
IFF DF-~CRIPTION OF THF DRAWINGS
Fig. 1 is an elevational view, partially in section, of an over-the-wire dilatation catheter having an inner tubular member embodying features of the invention.
Fig. 2 is a transverse cross section of the embodiment shown in Fig. 1 taken along the lines 2-2.
Fig. 3 is an elevational view, partially in section, of the distal section of a rapid exchange type dilatation catheter having an inner tubular member embodying features of the invention.
SUBST~TlJTE SHEET (R.,ILE ~6 CA 02243277 1998-07-1~
W 097/26027 PCT~US97/00843 - Fig. 4 is a transverse cross section of the embodiment shown in Fig. 4 taken along the line~ 5-5.
Fig. 5 is an elevational view, partially in section, of an alternative embodiment wherein the distai section of the catheter shaft is formed of an 5 extrusion of a polymerblend.
Fig. 6 is a transverse cross section of the embodiment shown in Fig. 6 taken along the lines 7-7.
nFTAI5 Fn DESCRIPTION OF THF INVFI~ITION
Reference is made to Figs. 1 and 2 which illustrate a balloon dilatation catheter 10 embodying features of the invention. Generally, the call ,eler 10 comprises an outer tubular member 1 1, an inner tubular member 12, a dilatation balloon 13 on a distal portion of the caLl,eter and ,an adapter 14 on the proximal end of the catheter. The inner tubular 15 member 12 has a guidewire receiving inner lumen 15 which slidably receives guidewire 16. The outer surface of the inner tubular member 12 and the inner surface of the outer tubular member 11 define an annular inflation lumen 17 which is in fluid communication with the interior of balloon 13 and side arm 18 of adapter 14.
SUBSTITUT~ SHEE~ ~IILE 26) CA 02243277 1998-07-1~
W O 97/26027 PCTrUS97/00843 The distal skirt 20 of balloon 13 is bonded, preferably fusion bonded, to the exterior of th~ inner tubular member 12 and the proximal skirt 21 is fusion bonded to the exterior of the outer tubular member 11.
The fusion bonds are preferably formed by applying laser energy to the 5 exterior of the skirts 20 and 21 which ca-lses the interface between the skirts and the exterior of the outer and inner tubular members 12 and 13.
In one presently preferred embodiment, both the outer and inner tubular members 11 and 12 are formed of a polymer blend in accordance with the invention.
Figs. 34 depict another embodiment of the invention directed to a rapid exchange type dilatation catheter 30. The catheter 30 includes a relatively stiff proximal shaft 31 formed of hypotubing and a relatively flexible distal shaft section 32. The distal shaft section 32 includes an inner tubular member 33, an outer tubular member 34 and a dilation balloon 35.
15 The inner tubular member 33 has a guidewire receiving inner lumen 36 which is in fluid communication with a distal guidewire port 37 in the distal end of the catheter 10 and a proximal guidewire port 38 disposed a short distance, e.g. about 10 to about 45 cm from the proximal end of the balloon 35. The proximal shaft 31 comprises a metallic hypotube 40 (e.g.
20 stainless steel or NiTi alloys) and an outer polymer jacket 41 formed of SUB~ITUTE SHEET ~ E ~6~
CA 02243277 1998-07-1~
suitable poiymer material such as high density polyethylene. The distal end 32 of the hypotube 40 is truncated and fits into the interior of the outer - tubular member 34 and bonded thereto by suitable adhesive 42. Support tube 43, preferably formed of polyimide, is disposed between the inner and outer tubular members 33 and 34 and defines inflation lumen 44. As shown in more detail in Figs. 4 and 5, the outer tubular member is partially bonded to the inner tubular member 33 and partially to the support tube 43.
A filler material 46, such as 75/25 high density/low density polyethylene, is disposed between the outer tubular member 34 and the support tube 43.
In the embodiment of Figs. 3-4 the inner tubular member 33 is rc ~" ,ed of a polymer blend in accordance with the present invention. The distal skirt 47 of balloon 35 is fusion bonded to the exterior of the inner tubular member 33 as in the previously discussed embodiment shown in Figs.1 and 2. The proximal skirt 48 of the balloon 35 forms the outer tubular member 34 and is formed of essentially the same material as the balloon. In an alternative embodiment not shown the outer tubular member 34 may be a member separate and distinct from the balloon and formed of a polymer blend in accordance with the present invention. In this latter case the proximal skirt of the balloon 35 is fusion bonded to the exterior of the outer tubular member.
SUB~TITl iTE SH~ R~JLE ~t3) CA 02243277 1998-07-1~
WO 97/26027 PCTrUS97/00843 - Figs. 5 and 6 illustrate yet another embodiment of the invention wherein the catheter 50 has a distal shaft 51 which is of a dual lumen construction and is formed by extruding a poiymer blend in accordance with the present invention. A tubuiar extension 52 extends 5 through the interior of the dilatation balloon 53 and has a distal guldewire port 54 in its distal end. The balloon 53 has a distal skirt 55 fusion bonded to the distal end of the tubular extension 52 and a proximal skirt 56 fusion bonded to the distal shaft 51 as shown in the drawings.
A presently preferred polymer blend includes about 65% high 10 density polyethylene, about 30% Hytrel(~) (available from Dupont) and about 5% ethylene methyl acrylate such as Lotryl 24MA005 (available from Elf ATOCHEM). This blend readily fusion bonds to polyethylene terephthalate and has a coefficient of friction of about 0.1-0.2.
Although individual features of embodiments of the invention 15 may be shown in some of the drawings and not in others, those skilled in the art will recognize that individual features of one embodiment of the invention can be combined with any or all the features of another embodiment. A variety of modifications can be made to the present invention without departing from the scope thereof.
SUBSTITUTE SHEET ~RU~E 2~3 . ' i~'t~.A; ,~-t=! ! - ~ ~yt~
Claims (15)
1. An intraluminal catheter having an elongated shaft which has proximal and distal portions and which has at least a catheter shaft segment thereof formed of a polymeric blend having a lubricious polymeric component and sufficient amounts of a bonding polymeric component so that the catheter shaft segment is lubricious and fusible with another catheter component.
2. The intraluminal catheter of claim 1 wherein the catheter component is formed of non-lubricious polymeric material.
3. The intraluminal catheter of claim 1 wherein the catheter component is a balloon.
4. The intraluminal catheter of claim 1 wherein the bonding polymeric component is compatibilized with the lubricious polymeric component by means of a compatiblizing agent.
5. The intraluminal catheter of claim 4 wherein the compatiblizing agent is a polymeric material formed at least in part of an acrylate monomer.
6. The intraluminal catheter of claim 4 wherein the compatiblizing agent is an alkyl acrylate such as ethylene methyl acrylate.
7. The intraluminal catheter of claim 1 wherein the lubricious polymeric component is polyethylene.
8. The intraluminal catheter of claim 1 wherein the lubricious polymeric component comprises at least 30% by weight of the polymeric blend.
9. The intraluminal catheter of claim 8 wherein the lubricious polymeric component comprises at least 50% by weight of the blend.
10. The intraluminal catheter of claim 1 wherein the bonding polymeric component of the polymeric blend is a co-polyester material.
11. The intraluminal catheter of claim 1 wherein the polymeric blend includes a catalytic material to facilitate cross linking in the catheter shaft segment.
12. The intraluminal catheter of claim 4 wherein the polymeric blend contains up to about 50% of the compatibilizing agent.
13. A balloon dilatation catheter comprising:
a) an elongated shaft which has proximal and distal portions and which has at least a catheter shaft segment thereof formed of a polymeric blend having a lubricious polymeric component and sufficient amounts of a bonding polymeric component so that the catheter shaft segment is lubricious and fusible with another catheter component; and b) a dilatation balloon formed of non-lubricious material having at least a distal skirt bonded to the catheter shaft segment.
a) an elongated shaft which has proximal and distal portions and which has at least a catheter shaft segment thereof formed of a polymeric blend having a lubricious polymeric component and sufficient amounts of a bonding polymeric component so that the catheter shaft segment is lubricious and fusible with another catheter component; and b) a dilatation balloon formed of non-lubricious material having at least a distal skirt bonded to the catheter shaft segment.
14. The balloon dilatation catheter of claim 13 wherein the distal skirt is fusion bonded to the catheter shaft segment.
15. The balloon dilatation catheter of claim 13 wherein the dilatation balloon is formed of polyethylene terephthalate.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US58733096A | 1996-01-16 | 1996-01-16 | |
| US08/587330 | 1996-01-16 | ||
| PCT/US1997/000843 WO1997026027A1 (en) | 1996-01-16 | 1997-01-16 | Lubricous and readily bondable catheter shaft |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2243277A1 true CA2243277A1 (en) | 1997-07-24 |
Family
ID=29422854
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002243277A Abandoned CA2243277A1 (en) | 1996-01-16 | 1997-01-16 | Lubricous and readily bondable catheter shaft |
Country Status (1)
| Country | Link |
|---|---|
| CA (1) | CA2243277A1 (en) |
-
1997
- 1997-01-16 CA CA002243277A patent/CA2243277A1/en not_active Abandoned
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| FZDE | Dead |