CA2216618C - Ball joint and introducer for vasoocclusive member - Google Patents
Ball joint and introducer for vasoocclusive member Download PDFInfo
- Publication number
- CA2216618C CA2216618C CA002216618A CA2216618A CA2216618C CA 2216618 C CA2216618 C CA 2216618C CA 002216618 A CA002216618 A CA 002216618A CA 2216618 A CA2216618 A CA 2216618A CA 2216618 C CA2216618 C CA 2216618C
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- Prior art keywords
- coil
- windings
- polymer
- lumen
- strand
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12131—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
- A61B17/1214—Coils or wires
- A61B17/1215—Coils or wires comprising additional materials, e.g. thrombogenic, having filaments, having fibers, being coated
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12131—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
- A61B17/1214—Coils or wires
- A61B17/12145—Coils or wires having a pre-set deployed three-dimensional shape
Abstract
A vasoocclusive helical metal coil having a thermoplastic polymer plug in at least one of its ends that has been melted so that it molds to the coil windings and insulates and blunts the end(s).
Description
OCT-31-01 15:04 FROM:SWABEY OGILVY RENAULT ID:416 216 0769 PAGE 2/2 BALL, JOYNT AND INTRODUCER FOR VASOOCCLTJSIVE MEMBE>(t TEC)EiNICAL FEED
This invention is in the field of vasooccIusion devices. More particularly, it relates to a vasoocclusion coil having a polymer tip.
13,A,CT~GROLTND
Vasoocclusion devices are surgical implements that are placed within vessels, typically via a catheter, to block tlae vessel or to f 11 a vascular cavity such as an aneurysm. One type of vasoocclusion device is iz~ the form of a helical wire coil. The coil zn:ay have a cylindrical, conical or other shaped envelope azzd may be formed into a secondary shape if desired. See U.S. Pat_ No. 4,994,069. The coil may have fibers attached to it to facilitate exnbolization. See U.S. Pats. Nos. 5,304,X94, 5,476,472 arid 5,382,259. The coil may be free (unattached) and placed at the desired vascular site by displacing it from the eztd of a catheter_ ,A.Itezxtatively, the coil may be removably attached to the distal end of a wire or fibez, placed at the desired site, and detached 1 S from the wire by mechanical, electrolytic, ox thermal means_ See U.S.
Pats.
Nos_ 4,735,201, 5,354,29S and 5,250,471.
One or both ends of tkze coil may be blunted to make it/them less likely to abrade or puncture the vessel. The "blunting" is typically accomplished by either melting the end or by soldering a bead of metal onto the end. Corrnx~only owned copending European application (IJP Publication No. 0 752 235), pubIisl~ed January 1, 1997, describes a coil having a polymer plug or insert in its distal ez~d_ The coil described in this copending application is used to transmit radiofrequency energy into the vessel to cause the vessEl wall to collapse. The polymer plug in the distal end of the coil insulates the tip of the coil and lessens the likelihood that the distal tip will erode or perforate the vessel wall.
A principal object of the present invention is to provide an easier and effective way to blunt and or insulate one or both ends of a vasoocclusive coil.
DISCLOSURE OF THE INVENTION
One aspect of the invention is a vasoocclusive coil comprising a helical coil having a multiplicity of windings that define a lumen, a first end, and a second end, and a plug of thermoplastic polymer comprised of a first portion that extends into the lumen at said first end and is molded into the windings defining said first end and a second rounded portion that extends axially outwardly from said lumen at said first end.
Another aspect is a method for blunting or insulating an end of a vasoocclusive coil comprising:
(a) providing a helical metal coil having a multiplicity of windings that define a lumen, a first end, and a second end;
(b) placing a first portion of a biocompatible thermoplastic polymer strand into the lumen at said first end with a second portion of said strand extending axially outwardly of the lumen at said first end;
(c) melting the polymer strand to cause said first portion to mold to the windings defining said first end and said second portion to be formed into a rounded protuberance; and (d) cooling the polymer strand to cause the strand to solidify.
BRIEF DESCRIPTION OF THE D AWINGS
In the drawings, which are not to scale, Figure 1 is an elevational view of one embodiment of the invention in which a helical coil is blunted at one end.
Figure 2 is an elevational view of another embodiment of the invention in which a helical coil having a secondary shape is blunted at both ends.
This invention is in the field of vasooccIusion devices. More particularly, it relates to a vasoocclusion coil having a polymer tip.
13,A,CT~GROLTND
Vasoocclusion devices are surgical implements that are placed within vessels, typically via a catheter, to block tlae vessel or to f 11 a vascular cavity such as an aneurysm. One type of vasoocclusion device is iz~ the form of a helical wire coil. The coil zn:ay have a cylindrical, conical or other shaped envelope azzd may be formed into a secondary shape if desired. See U.S. Pat_ No. 4,994,069. The coil may have fibers attached to it to facilitate exnbolization. See U.S. Pats. Nos. 5,304,X94, 5,476,472 arid 5,382,259. The coil may be free (unattached) and placed at the desired vascular site by displacing it from the eztd of a catheter_ ,A.Itezxtatively, the coil may be removably attached to the distal end of a wire or fibez, placed at the desired site, and detached 1 S from the wire by mechanical, electrolytic, ox thermal means_ See U.S.
Pats.
Nos_ 4,735,201, 5,354,29S and 5,250,471.
One or both ends of tkze coil may be blunted to make it/them less likely to abrade or puncture the vessel. The "blunting" is typically accomplished by either melting the end or by soldering a bead of metal onto the end. Corrnx~only owned copending European application (IJP Publication No. 0 752 235), pubIisl~ed January 1, 1997, describes a coil having a polymer plug or insert in its distal ez~d_ The coil described in this copending application is used to transmit radiofrequency energy into the vessel to cause the vessEl wall to collapse. The polymer plug in the distal end of the coil insulates the tip of the coil and lessens the likelihood that the distal tip will erode or perforate the vessel wall.
A principal object of the present invention is to provide an easier and effective way to blunt and or insulate one or both ends of a vasoocclusive coil.
DISCLOSURE OF THE INVENTION
One aspect of the invention is a vasoocclusive coil comprising a helical coil having a multiplicity of windings that define a lumen, a first end, and a second end, and a plug of thermoplastic polymer comprised of a first portion that extends into the lumen at said first end and is molded into the windings defining said first end and a second rounded portion that extends axially outwardly from said lumen at said first end.
Another aspect is a method for blunting or insulating an end of a vasoocclusive coil comprising:
(a) providing a helical metal coil having a multiplicity of windings that define a lumen, a first end, and a second end;
(b) placing a first portion of a biocompatible thermoplastic polymer strand into the lumen at said first end with a second portion of said strand extending axially outwardly of the lumen at said first end;
(c) melting the polymer strand to cause said first portion to mold to the windings defining said first end and said second portion to be formed into a rounded protuberance; and (d) cooling the polymer strand to cause the strand to solidify.
BRIEF DESCRIPTION OF THE D AWINGS
In the drawings, which are not to scale, Figure 1 is an elevational view of one embodiment of the invention in which a helical coil is blunted at one end.
Figure 2 is an elevational view of another embodiment of the invention in which a helical coil having a secondary shape is blunted at both ends.
Figure 3 is an elevational view of a third embodiment of the invention in which the helical coil has a multiplicity of fibrous elements attached to it.
Figure 4 is an elevational view of another embodiment of the invention wherein the coil includes a radially extending fibrous element.
Figure 5 is an elevational view of a fourth embodiment of the invention in which the helical coil is adapted to be mechanically released from the distal end of a wire.
Figure 6 is an elevational view of a fifth embodiment of the invention in which the helical coil is adapted to be electrolytically released from the distal end of a wire.
MODES FOR CARRYING OUT THE INVENTION
i~ iburv i ~l~pi~ts unc e;mbodimcnt, ~;encrally clesi~namci 1 U ui a va~uucciusive coil of this invention. Coil 10 has a multiplicity of helical windings 11. The windings of the end segments, generally designated 12 and 13 of the coil have a longer pitch than the windings of the central segment 14. The coil has two free ends, generally designated 1 S and 16, each of which is blunted by a plug 17 of a biocompatible thermoplastic polymer. As depicted, plug 17 has an inner section that extends into the lumen 19 defined~by the windings and an outer portion 20 that extends outwardly from the lumen and defines a rounded blunt protuberance. The inner section 18 is thermally molded to the windings; that is, it at least partly surrounds the windings and conforms to the shape of the windings. In such structure, the plug is less likely to loosen or disengage from the windings than the structure shown in EP 0 752 235. The inner section will normally extend about 1 to 5 windings into the lumen 19, preferably about 2-4 windings.
The windings of coil 10 will typically be made of a metal such as platinum, gold, rhodium, rhenium, palladium, tungsten, and the like or alloys of such metals.
Figure 4 is an elevational view of another embodiment of the invention wherein the coil includes a radially extending fibrous element.
Figure 5 is an elevational view of a fourth embodiment of the invention in which the helical coil is adapted to be mechanically released from the distal end of a wire.
Figure 6 is an elevational view of a fifth embodiment of the invention in which the helical coil is adapted to be electrolytically released from the distal end of a wire.
MODES FOR CARRYING OUT THE INVENTION
i~ iburv i ~l~pi~ts unc e;mbodimcnt, ~;encrally clesi~namci 1 U ui a va~uucciusive coil of this invention. Coil 10 has a multiplicity of helical windings 11. The windings of the end segments, generally designated 12 and 13 of the coil have a longer pitch than the windings of the central segment 14. The coil has two free ends, generally designated 1 S and 16, each of which is blunted by a plug 17 of a biocompatible thermoplastic polymer. As depicted, plug 17 has an inner section that extends into the lumen 19 defined~by the windings and an outer portion 20 that extends outwardly from the lumen and defines a rounded blunt protuberance. The inner section 18 is thermally molded to the windings; that is, it at least partly surrounds the windings and conforms to the shape of the windings. In such structure, the plug is less likely to loosen or disengage from the windings than the structure shown in EP 0 752 235. The inner section will normally extend about 1 to 5 windings into the lumen 19, preferably about 2-4 windings.
The windings of coil 10 will typically be made of a metal such as platinum, gold, rhodium, rhenium, palladium, tungsten, and the like or alloys of such metals.
These metals have significant radiopacity and their alloys may be tailored to provide desired degrees of stiffness and flexibility. The windings may be made of other suitable biocompatible materials such as polymers or composites of metals and polymers.
While the cross-section of the windings of Figure 1 is circular, windings having other cross-sectional shapes, e.g. elliptical, trapezoidal, rhombic, rectangular, square, may be used. Circular cross sectional windings will typically have a diameter of about 0.01 to about 0.15 mm. Correspondingly, the diameter of the helix formed by the windings will normally be in the range of about 0.2 to 0.8 mm. For neurovascular use the diameter of the helix will typically be in the range of 0.3 to 0.5 mm. While the helix is shown as having a uniform diameter along the length of the coil, helixes having a varying diameter over a portion or the entire length of the helix or helixes having segments of different diameter may also be used.
Similarly, the pitch of the windings may be uniform, as shown in Figure 4, or may vary over a 1 S portion or the entire length of the coil. The axial length of the coil will usually be in the range of 0.5 to 100 cm, more usually 2 to 40 cm. The coil will typically have 10 to 75 windings per cm, more usually 10 to 40 windings per cm. It will be appreciated that the above described dimensions are not critical and that dimensions that are suitable for occluding vascular sites within the human body are intended.
The plug 17 is made of a thermoplastic, biocompatible polymer such as a polyester (e.g. Dacron), polyamide (e.g. Nylon), or polyolefin (e.g., polypropylene).
Typically the polymer will melt at temperatures above about 125°C. The plug is formed by initially placing a rod or strand of the polymer into the lumen of the coil, leaving a portion (typically about 0.1 to 3 mm) of the rod or strand extending outwardly from the coil end. The plug is then heated to above the melt temperature of the polymer causing the portion of the rod within the lumen to flow and mold to the coil windings anal the portion of the rod outside the lumen to form into a rounded bead or protuberance. The plug is then cooled to solidify the polymer.
Figure 2 depicts another embodiment, generally designated 30, of a vasoocclusive coil of the invention. Coil 30 has a similar structure to coil 10 except that the former has a uniform pitch and a clover leaf secondary shape. As depicted, the ends 31, 32 of coil 30 are blunted with polymer plugs or tips 33, 34.
Figure 3 shoms a third embodiment, generally designated 40, of a vasoocclusive coil of the invention. Coil 40 has a similar structure to coil 10 except that the former has a uniform pitch and includes a plurality of fibers 41 attached to the coil windings. As shown, end 42 of coil 40 is blunted with a polymer plug 43.
Figure 4 shows a coil 44 that is identical in structure to the coil of Figure except that a strand 4:5 of polymer extends sinusoidally the length of the coil with its respective ends fused to and integral with the polymer tips. As shown, the strand is composed of loops that extend radially outwardly of the coil windings and extend through the coil windings at: spaced intervals.
The vasoocclusive coils of the invention are particularly useful in devices, such as those described in E,P 0 752 235, that are used to deliver radiofrequency energy intravascularly. The coil may be nondetachable or detachable by electrolytic means such as described in U.S. Pat. No. 5,122,136 or by mechanical means such as described in U.S. Pate,. Nos. 5,234,437; 5,250,071; 5,261,916; 5,304,195;
While the cross-section of the windings of Figure 1 is circular, windings having other cross-sectional shapes, e.g. elliptical, trapezoidal, rhombic, rectangular, square, may be used. Circular cross sectional windings will typically have a diameter of about 0.01 to about 0.15 mm. Correspondingly, the diameter of the helix formed by the windings will normally be in the range of about 0.2 to 0.8 mm. For neurovascular use the diameter of the helix will typically be in the range of 0.3 to 0.5 mm. While the helix is shown as having a uniform diameter along the length of the coil, helixes having a varying diameter over a portion or the entire length of the helix or helixes having segments of different diameter may also be used.
Similarly, the pitch of the windings may be uniform, as shown in Figure 4, or may vary over a 1 S portion or the entire length of the coil. The axial length of the coil will usually be in the range of 0.5 to 100 cm, more usually 2 to 40 cm. The coil will typically have 10 to 75 windings per cm, more usually 10 to 40 windings per cm. It will be appreciated that the above described dimensions are not critical and that dimensions that are suitable for occluding vascular sites within the human body are intended.
The plug 17 is made of a thermoplastic, biocompatible polymer such as a polyester (e.g. Dacron), polyamide (e.g. Nylon), or polyolefin (e.g., polypropylene).
Typically the polymer will melt at temperatures above about 125°C. The plug is formed by initially placing a rod or strand of the polymer into the lumen of the coil, leaving a portion (typically about 0.1 to 3 mm) of the rod or strand extending outwardly from the coil end. The plug is then heated to above the melt temperature of the polymer causing the portion of the rod within the lumen to flow and mold to the coil windings anal the portion of the rod outside the lumen to form into a rounded bead or protuberance. The plug is then cooled to solidify the polymer.
Figure 2 depicts another embodiment, generally designated 30, of a vasoocclusive coil of the invention. Coil 30 has a similar structure to coil 10 except that the former has a uniform pitch and a clover leaf secondary shape. As depicted, the ends 31, 32 of coil 30 are blunted with polymer plugs or tips 33, 34.
Figure 3 shoms a third embodiment, generally designated 40, of a vasoocclusive coil of the invention. Coil 40 has a similar structure to coil 10 except that the former has a uniform pitch and includes a plurality of fibers 41 attached to the coil windings. As shown, end 42 of coil 40 is blunted with a polymer plug 43.
Figure 4 shows a coil 44 that is identical in structure to the coil of Figure except that a strand 4:5 of polymer extends sinusoidally the length of the coil with its respective ends fused to and integral with the polymer tips. As shown, the strand is composed of loops that extend radially outwardly of the coil windings and extend through the coil windings at: spaced intervals.
The vasoocclusive coils of the invention are particularly useful in devices, such as those described in E,P 0 752 235, that are used to deliver radiofrequency energy intravascularly. The coil may be nondetachable or detachable by electrolytic means such as described in U.S. Pat. No. 5,122,136 or by mechanical means such as described in U.S. Pate,. Nos. 5,234,437; 5,250,071; 5,261,916; 5,304,195;
5,312,415;
and 5,350,397.
Figure 5 depicts an embodiment, generally designated 50, having a coil 51 that may be detached through operation of a connective joint 52. Joint 52 has a clasp section 53 which remains attached to a core wire 54 when sheath or catheter body 55 is retracted proximall~r. Joint 52 also includes a second clasp section 56 that is carried on the proxim~~l end of coil 51 and interlocks with clasp section 53 when the assembly is within sheath 5-'i. When the sheath is withdrawn from about the assembly, the clasp sections are free to disengage, thus detaching coil 51. As shown, the distal end of coil 51 has a polymer plug 57 that blunts and insulates the distal end.
Core wire 51 may be electrically connected to a source of radiofrequency energy.
Figure 6 shows an embodiment, generally designated 60, having a coil 61 that may be detached through operation of a connective joint 62 that is susceptible to electrolysis. Such joints are described in detail in U.S. Pat. No. 5,423,829.
Joint 62 is made of a metal which, upon application of a suitable voltage to a core wire 63, will erode in the bloodstream, thereby allowing coil 61 to detach. Coil 61 is made of a metal that is more "noble" in the electromotive series than the metal of joint 62. A
return electrode (not shown) is supplied to complete the circuit. The region of core wire 63 proximal to the joint is insulated to focus the erosion at the joint.
An electrically conductive bushing 66 is used to connect the distal end of core wire 63 to the proximal end of coil 61. A polymer plug 68, similar in structure to the previously described plugs, is molded into the distal end of the coil. In addition, the exterior surface of the distal windings of the coil is encased in a thermoplastic polymer sheath 69. As shown, the polymer sheath is molded to the windings and is integral with the plug 68. This structure may be formed by placing a thermoplastic sheath about the distal windings, placing a strand of thermoplastic polymer in the distal end of the coil, and heating the distal end of the coil to cause the sheath and strands to melt, fuse together, and mold to the interior and exterior surfaces of the windings.
and 5,350,397.
Figure 5 depicts an embodiment, generally designated 50, having a coil 51 that may be detached through operation of a connective joint 52. Joint 52 has a clasp section 53 which remains attached to a core wire 54 when sheath or catheter body 55 is retracted proximall~r. Joint 52 also includes a second clasp section 56 that is carried on the proxim~~l end of coil 51 and interlocks with clasp section 53 when the assembly is within sheath 5-'i. When the sheath is withdrawn from about the assembly, the clasp sections are free to disengage, thus detaching coil 51. As shown, the distal end of coil 51 has a polymer plug 57 that blunts and insulates the distal end.
Core wire 51 may be electrically connected to a source of radiofrequency energy.
Figure 6 shows an embodiment, generally designated 60, having a coil 61 that may be detached through operation of a connective joint 62 that is susceptible to electrolysis. Such joints are described in detail in U.S. Pat. No. 5,423,829.
Joint 62 is made of a metal which, upon application of a suitable voltage to a core wire 63, will erode in the bloodstream, thereby allowing coil 61 to detach. Coil 61 is made of a metal that is more "noble" in the electromotive series than the metal of joint 62. A
return electrode (not shown) is supplied to complete the circuit. The region of core wire 63 proximal to the joint is insulated to focus the erosion at the joint.
An electrically conductive bushing 66 is used to connect the distal end of core wire 63 to the proximal end of coil 61. A polymer plug 68, similar in structure to the previously described plugs, is molded into the distal end of the coil. In addition, the exterior surface of the distal windings of the coil is encased in a thermoplastic polymer sheath 69. As shown, the polymer sheath is molded to the windings and is integral with the plug 68. This structure may be formed by placing a thermoplastic sheath about the distal windings, placing a strand of thermoplastic polymer in the distal end of the coil, and heating the distal end of the coil to cause the sheath and strands to melt, fuse together, and mold to the interior and exterior surfaces of the windings.
Claims (13)
1. A vasoocclusion coil comprising a helical coil having a multiplicity of windings that define a lumen, a first end and a second end, and a plug of thermoplastic biocompatible polymer comprised of a first portion that extends into the lumen at said first end and is molded into the windings defining said first end and a second rounded portion that extends axially outwardly from said lumen at said first end.
2. The vasoocclusion coil of claim 1 wherein the polymer is a polyester.
3. The vasoocclusion coil of claim 1 wherein the windings are made of metal.
4. The vasoocclusion coil of claim 1 wherein said first portion extends 1 to
5 windings into the lumen.
5. The vasoocclusion coil of claim 1 including a sheath of a thermoplastic biocompatible polymer that encases and is molded to the exterior surface of the windings defining the first end.
5. The vasoocclusion coil of claim 1 including a sheath of a thermoplastic biocompatible polymer that encases and is molded to the exterior surface of the windings defining the first end.
6. The vasoocclusion coil of claim 1 further comprising a strand of said polymer having a first end connected to the first portion of the plug, a second end, and a segment intermediate said first and second ends that extends axially along the coil in a generally serpentine configuration composed of loops that extend through the coil windings at spaced intervals.
7. The vasoocclusion coil of claim 1 further comprising a second plug of thermoplastic biocompatible polymer comprised of a first portion that extends into the lumen at said second end of the coil and is molded into the windings defining said second end and a second rounded portion that extends axially outwardly from saidlumen at said second end.
8. The vasoocclusion coil of claim 7 comprising a strand of a biocompatible polymer having a first end connected to said first plug, a second end connected to said second plug, and a segment intermediate said first and second ends of the strand that extends axially along the coil in a generally serpentine configuration composed of loops that extend through the coil windings at spaced intervals.
9. An assembly for use in occluding a vessel or vascular cavity comprising:
(a) a wire having a distal end;
(b) the vasoocclusion coil of claim 1 wherein the distal end of the wire is detachably coupled to the second end of the coil.
(a) a wire having a distal end;
(b) the vasoocclusion coil of claim 1 wherein the distal end of the wire is detachably coupled to the second end of the coil.
10. The assembly of claim 9 wherein the distal end of the wire is coupled to the second end of the coil by a mechanically detachable joint.
11. The assembly of claim 9 wherein the distal end of the wire is coupled to the second end of the coil by a metal joint that is susceptible to electrolysis.
12. A method for blunting and insulating an end of a vasoocclusion coil comprising:
(a) providing a helical metal coil having a multiplicity of windings that define a lumen, a first end, and a second end;
(b) placing a first portion of a biocompatible thermoplastic polymer strand into the lumen at said first end with a second portion of said strand extending axially outwardly of the lumen at said first end;
(c) melting the polymer strand to cause the first portion to mold to the windings defining said first end and said second portion to be formed into a rounded protuberance, and (d) cooling the polymer strand to cause the polymer to solidify.
(a) providing a helical metal coil having a multiplicity of windings that define a lumen, a first end, and a second end;
(b) placing a first portion of a biocompatible thermoplastic polymer strand into the lumen at said first end with a second portion of said strand extending axially outwardly of the lumen at said first end;
(c) melting the polymer strand to cause the first portion to mold to the windings defining said first end and said second portion to be formed into a rounded protuberance, and (d) cooling the polymer strand to cause the polymer to solidify.
13. The method of claim 12 including the steps of placing a sheath of a thermoplastic biocompatible polymer about the windings defining said first end and melting said sheath to cause the sheath to mold to the windings and fuse with the strand.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/721,351 US5690667A (en) | 1996-09-26 | 1996-09-26 | Vasoocclusion coil having a polymer tip |
| US08/721,351 | 1996-09-26 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2216618A1 CA2216618A1 (en) | 1998-03-26 |
| CA2216618C true CA2216618C (en) | 2002-01-08 |
Family
ID=24897624
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002216618A Expired - Fee Related CA2216618C (en) | 1996-09-26 | 1997-09-26 | Ball joint and introducer for vasoocclusive member |
Country Status (10)
| Country | Link |
|---|---|
| US (1) | US5690667A (en) |
| EP (1) | EP0832606B1 (en) |
| JP (1) | JP3102855B2 (en) |
| KR (1) | KR19980025045A (en) |
| AT (1) | ATE241934T1 (en) |
| AU (1) | AU689070B1 (en) |
| CA (1) | CA2216618C (en) |
| DE (1) | DE69722545T2 (en) |
| ES (1) | ES2198535T3 (en) |
| NO (1) | NO974436L (en) |
Families Citing this family (135)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DK0754435T3 (en) * | 1995-06-30 | 2000-11-27 | Target Therapeutics Inc | Stretch-resistant co-occlusion spirals |
| US6013084A (en) | 1995-06-30 | 2000-01-11 | Target Therapeutics, Inc. | Stretch resistant vaso-occlusive coils (II) |
| US6320384B1 (en) * | 1996-12-23 | 2001-11-20 | David F. Doty | Thermal buffering of cross-coils in high-power NMR decoupling |
| US5830230A (en) * | 1997-03-07 | 1998-11-03 | Micro Therapeutics, Inc. | Method of intracranial vascular embolotherapy using self anchoring coils |
| US6136015A (en) * | 1998-08-25 | 2000-10-24 | Micrus Corporation | Vasoocclusive coil |
| US6159165A (en) | 1997-12-05 | 2000-12-12 | Micrus Corporation | Three dimensional spherical micro-coils manufactured from radiopaque nickel-titanium microstrand |
| US6168570B1 (en) | 1997-12-05 | 2001-01-02 | Micrus Corporation | Micro-strand cable with enhanced radiopacity |
| US6113622A (en) * | 1998-03-10 | 2000-09-05 | Cordis Corporation | Embolic coil hydraulic deployment system |
| US6379374B1 (en) | 1998-10-22 | 2002-04-30 | Cordis Neurovascular, Inc. | Small diameter embolic coil hydraulic deployment system |
| US6068644A (en) * | 1998-03-10 | 2000-05-30 | Cordis Corporation | Embolic coil hydraulic deployment system having improved catheter |
| US6063100A (en) * | 1998-03-10 | 2000-05-16 | Cordis Corporation | Embolic coil deployment system with improved embolic coil |
| US6168615B1 (en) | 1998-05-04 | 2001-01-02 | Micrus Corporation | Method and apparatus for occlusion and reinforcement of aneurysms |
| US6277126B1 (en) * | 1998-10-05 | 2001-08-21 | Cordis Neurovascular Inc. | Heated vascular occlusion coil development system |
| AU6288799A (en) * | 1998-10-09 | 2000-05-01 | Cook Incorporated | Vasoocclusion coil device having a core therein |
| US6254612B1 (en) | 1998-10-22 | 2001-07-03 | Cordis Neurovascular, Inc. | Hydraulic stent deployment system |
| US6383204B1 (en) | 1998-12-15 | 2002-05-07 | Micrus Corporation | Variable stiffness coil for vasoocclusive devices |
| EP1992308B1 (en) | 1999-06-02 | 2015-10-28 | Microtransform, Inc. | Intracorporeal occlusive device |
| US6602261B2 (en) | 1999-10-04 | 2003-08-05 | Microvention, Inc. | Filamentous embolic device with expansile elements |
| US8048104B2 (en) | 2000-10-30 | 2011-11-01 | Dendron Gmbh | Device for the implantation of occlusion spirals |
| US6616591B1 (en) * | 1999-12-08 | 2003-09-09 | Scimed Life Systems, Inc. | Radioactive compositions and methods of use thereof |
| US6331184B1 (en) | 1999-12-10 | 2001-12-18 | Scimed Life Systems, Inc. | Detachable covering for an implantable medical device |
| US6544225B1 (en) | 2000-02-29 | 2003-04-08 | Cordis Neurovascular, Inc. | Embolic coil hydraulic deployment system with purge mechanism |
| US7029486B2 (en) * | 2000-09-26 | 2006-04-18 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| US7033374B2 (en) * | 2000-09-26 | 2006-04-25 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| US6605101B1 (en) * | 2000-09-26 | 2003-08-12 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| EP1401338B1 (en) * | 2001-05-29 | 2011-07-20 | Microvention, Inc. | Method of manufacturing expansile filamentous embolization devices |
| US20030014075A1 (en) * | 2001-07-16 | 2003-01-16 | Microvention, Inc. | Methods, materials and apparatus for deterring or preventing endoleaks following endovascular graft implanation |
| US8252040B2 (en) | 2001-07-20 | 2012-08-28 | Microvention, Inc. | Aneurysm treatment device and method of use |
| EP1448105B1 (en) | 2001-11-07 | 2009-12-23 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| US7485122B2 (en) * | 2002-06-27 | 2009-02-03 | Boston Scientific Scimed, Inc. | Integrated anchor coil in stretch-resistant vaso-occlusive coils |
| DE10233085B4 (en) | 2002-07-19 | 2014-02-20 | Dendron Gmbh | Stent with guide wire |
| US8425549B2 (en) | 2002-07-23 | 2013-04-23 | Reverse Medical Corporation | Systems and methods for removing obstructive matter from body lumens and treating vascular defects |
| CN101919722A (en) | 2002-07-31 | 2010-12-22 | 微温森公司 | The vascular occluding device of three-part coaxial |
| US20050171572A1 (en) * | 2002-07-31 | 2005-08-04 | Microvention, Inc. | Multi-layer coaxial vaso-occlusive device |
| US7648509B2 (en) | 2003-03-10 | 2010-01-19 | Ilion Medical Llc | Sacroiliac joint immobilization |
| CA2530992C (en) | 2003-07-03 | 2012-01-03 | Cook, Inc. | Occluding device for occluding fluid flow through a body vessel |
| US8043321B2 (en) * | 2003-07-24 | 2011-10-25 | Boston Scientific Scimed, Inc. | Embolic coil |
| US20050065501A1 (en) * | 2003-09-23 | 2005-03-24 | Scimed Life Systems, Inc. | Energy activated vaso-occlusive devices |
| US20070104752A1 (en) * | 2003-12-10 | 2007-05-10 | Lee Jeffrey A | Aneurysm embolization material and device |
| DE102004003265A1 (en) * | 2004-01-21 | 2005-08-11 | Dendron Gmbh | Device for the implantation of electrically isolated occlusion coils |
| US7785348B2 (en) * | 2004-05-14 | 2010-08-31 | Ethicon Endo-Surgery, Inc. | Devices and methods of locking and cutting a suture in a medical procedure |
| US20060025802A1 (en) * | 2004-07-30 | 2006-02-02 | Sowers William W | Embolic coil delivery system with U-shaped fiber release mechanism |
| US7918872B2 (en) | 2004-07-30 | 2011-04-05 | Codman & Shurtleff, Inc. | Embolic device delivery system with retractable partially coiled-fiber release |
| ATE448737T1 (en) | 2004-09-22 | 2009-12-15 | Dendron Gmbh | DEVICE FOR IMPLANTING MICROWL COILS |
| US7879064B2 (en) | 2004-09-22 | 2011-02-01 | Micro Therapeutics, Inc. | Medical implant |
| WO2006042114A1 (en) | 2004-10-06 | 2006-04-20 | Cook, Inc. | Emboli capturing device having a coil and method for capturing emboli |
| US8262720B2 (en) * | 2004-12-02 | 2012-09-11 | Nitinol Development Corporation | Prosthesis comprising dual tapered stent |
| US20060155323A1 (en) | 2005-01-07 | 2006-07-13 | Porter Stephen C | Intra-aneurysm devices |
| US8945169B2 (en) | 2005-03-15 | 2015-02-03 | Cook Medical Technologies Llc | Embolic protection device |
| US8221446B2 (en) | 2005-03-15 | 2012-07-17 | Cook Medical Technologies | Embolic protection device |
| US7955344B2 (en) * | 2005-04-01 | 2011-06-07 | Nexgen Medical Systems, Inc. | Thrombus removal system and process |
| US7955345B2 (en) * | 2005-04-01 | 2011-06-07 | Nexgen Medical Systems, Inc. | Thrombus removal system and process |
| DE102005019782A1 (en) * | 2005-04-28 | 2006-11-09 | Dendron Gmbh | Device for implantation of occlusion coils with internal securing means |
| US7850708B2 (en) | 2005-06-20 | 2010-12-14 | Cook Incorporated | Embolic protection device having a reticulated body with staggered struts |
| US8109962B2 (en) | 2005-06-20 | 2012-02-07 | Cook Medical Technologies Llc | Retrievable device having a reticulation portion with staggered struts |
| US8109913B2 (en) * | 2005-07-11 | 2012-02-07 | Dsm Ip Assets B.V. | Coiled wire for the controlled release of drugs to the eye |
| US7771452B2 (en) | 2005-07-12 | 2010-08-10 | Cook Incorporated | Embolic protection device with a filter bag that disengages from a basket |
| US7766934B2 (en) | 2005-07-12 | 2010-08-03 | Cook Incorporated | Embolic protection device with an integral basket and bag |
| US8187298B2 (en) | 2005-08-04 | 2012-05-29 | Cook Medical Technologies Llc | Embolic protection device having inflatable frame |
| ES2368589T3 (en) * | 2005-08-31 | 2011-11-18 | Cook Medical Technologies Llc | CATHETER FOR THE IMPLEMENTATION OF ENDOPROOTHESIS. |
| US8377092B2 (en) | 2005-09-16 | 2013-02-19 | Cook Medical Technologies Llc | Embolic protection device |
| US8632562B2 (en) | 2005-10-03 | 2014-01-21 | Cook Medical Technologies Llc | Embolic protection device |
| US8182508B2 (en) | 2005-10-04 | 2012-05-22 | Cook Medical Technologies Llc | Embolic protection device |
| US8252017B2 (en) | 2005-10-18 | 2012-08-28 | Cook Medical Technologies Llc | Invertible filter for embolic protection |
| US8216269B2 (en) | 2005-11-02 | 2012-07-10 | Cook Medical Technologies Llc | Embolic protection device having reduced profile |
| US8152831B2 (en) | 2005-11-17 | 2012-04-10 | Cook Medical Technologies Llc | Foam embolic protection device |
| US20070225738A1 (en) * | 2006-03-24 | 2007-09-27 | Cook Incorporated | Aneurysm coil and method of assembly |
| US8777979B2 (en) | 2006-04-17 | 2014-07-15 | Covidien Lp | System and method for mechanically positioning intravascular implants |
| CA2649702C (en) | 2006-04-17 | 2014-12-09 | Microtherapeutics, Inc. | System and method for mechanically positioning intravascular implants |
| CN101500623B (en) | 2006-06-15 | 2016-08-24 | 微温森公司 | A kind of embolization device being made up of expandable polymer |
| US20080046092A1 (en) * | 2006-08-17 | 2008-02-21 | Richard Champion Davis | Coil embolization device with stretch resistance fiber |
| US20080071307A1 (en) | 2006-09-19 | 2008-03-20 | Cook Incorporated | Apparatus and methods for in situ embolic protection |
| US20080269774A1 (en) | 2006-10-26 | 2008-10-30 | Chestnut Medical Technologies, Inc. | Intracorporeal Grasping Device |
| US9901434B2 (en) | 2007-02-27 | 2018-02-27 | Cook Medical Technologies Llc | Embolic protection device including a Z-stent waist band |
| KR20100015521A (en) | 2007-03-13 | 2010-02-12 | 마이크로 테라퓨틱스 인코포레이티드 | An implant, a mandrel, and a method of forming an implant |
| KR20100015520A (en) | 2007-03-13 | 2010-02-12 | 마이크로 테라퓨틱스 인코포레이티드 | An implant including a coil and a stretch-resistant member |
| WO2009003049A2 (en) | 2007-06-25 | 2008-12-31 | Micro Vention, Inc. | Self-expanding prosthesis |
| CA2696629C (en) | 2007-08-17 | 2016-01-19 | Micrus Endovascular Corporation | A twisted primary coil for vascular therapy |
| US9138307B2 (en) | 2007-09-14 | 2015-09-22 | Cook Medical Technologies Llc | Expandable device for treatment of a stricture in a body vessel |
| US8252018B2 (en) | 2007-09-14 | 2012-08-28 | Cook Medical Technologies Llc | Helical embolic protection device |
| US8419748B2 (en) | 2007-09-14 | 2013-04-16 | Cook Medical Technologies Llc | Helical thrombus removal device |
| US8088140B2 (en) | 2008-05-19 | 2012-01-03 | Mindframe, Inc. | Blood flow restorative and embolus removal methods |
| US11337714B2 (en) | 2007-10-17 | 2022-05-24 | Covidien Lp | Restoring blood flow and clot removal during acute ischemic stroke |
| EP2266639B1 (en) | 2007-12-21 | 2016-10-05 | MicroVention, Inc. | Methods for preparing hydrogel filaments for biomedical use |
| EP2234562B1 (en) | 2007-12-21 | 2019-02-27 | MicroVention, Inc. | A system and method of detecting implant detachment |
| JP5366974B2 (en) | 2007-12-21 | 2013-12-11 | マイクロベンション インコーポレイテッド | System and method for determining the position of a separation zone of a separable implant |
| KR101819554B1 (en) | 2008-02-22 | 2018-01-17 | 마이크로 테라퓨틱스 인코포레이티드 | Methods and apparatus for flow restoration |
| US8740912B2 (en) | 2008-02-27 | 2014-06-03 | Ilion Medical Llc | Tools for performing less invasive orthopedic joint procedures |
| US10716573B2 (en) | 2008-05-01 | 2020-07-21 | Aneuclose | Janjua aneurysm net with a resilient neck-bridging portion for occluding a cerebral aneurysm |
| US10028747B2 (en) | 2008-05-01 | 2018-07-24 | Aneuclose Llc | Coils with a series of proximally-and-distally-connected loops for occluding a cerebral aneurysm |
| US8388644B2 (en) | 2008-12-29 | 2013-03-05 | Cook Medical Technologies Llc | Embolic protection device and method of use |
| AU2010298026B2 (en) * | 2009-09-24 | 2015-11-05 | Microvention, Inc. | Injectable hydrogel filaments for biomedical uses |
| KR101745748B1 (en) | 2009-10-26 | 2017-06-12 | 마이크로벤션, 인코포레이티드 | Embolization device constructed from expansile polymer |
| US9358140B1 (en) | 2009-11-18 | 2016-06-07 | Aneuclose Llc | Stent with outer member to embolize an aneurysm |
| EP2555690B1 (en) * | 2010-04-05 | 2014-07-02 | Boston Scientific Scimed, Inc. | Vaso-occlusive devices |
| KR20130054952A (en) | 2010-04-14 | 2013-05-27 | 마이크로벤션, 인코포레이티드 | Implant delivery device |
| US9039749B2 (en) | 2010-10-01 | 2015-05-26 | Covidien Lp | Methods and apparatuses for flow restoration and implanting members in the human body |
| US9456823B2 (en) | 2011-04-18 | 2016-10-04 | Terumo Corporation | Embolic devices |
| US10137280B2 (en) | 2011-06-30 | 2018-11-27 | Incube Labs, Llc | System and method for treatment of hemorrhagic stroke |
| US9033956B2 (en) | 2011-09-06 | 2015-05-19 | Cook Medical Technologies Llc | Electrically charged medical device |
| US9579104B2 (en) | 2011-11-30 | 2017-02-28 | Covidien Lp | Positioning and detaching implants |
| US9011480B2 (en) | 2012-01-20 | 2015-04-21 | Covidien Lp | Aneurysm treatment coils |
| WO2013119332A2 (en) | 2012-02-09 | 2013-08-15 | Stout Medical Group, L.P. | Embolic device and methods of use |
| US9687245B2 (en) | 2012-03-23 | 2017-06-27 | Covidien Lp | Occlusive devices and methods of use |
| WO2013158781A1 (en) | 2012-04-18 | 2013-10-24 | Microvention, Inc. | Embolic devices |
| US9326774B2 (en) | 2012-08-03 | 2016-05-03 | Covidien Lp | Device for implantation of medical devices |
| CA2904862A1 (en) | 2013-03-14 | 2014-10-02 | Incumedx Inc. | Implants, methods of manufacturing the same, and devices and methods for delivering the implants to a vascular disorder of a patient |
| CN105530986A (en) | 2013-05-08 | 2016-04-27 | 埃姆博尔克斯公司 | Device and methods for transvascular tumor embolization with integrated flow regulation |
| US9844383B2 (en) | 2013-05-08 | 2017-12-19 | Embolx, Inc. | Devices and methods for low pressure tumor embolization |
| CN105899150B (en) | 2013-07-31 | 2018-07-27 | Neuvt 有限公司 | Method and apparatus for Endovascular Embolization |
| US10010328B2 (en) | 2013-07-31 | 2018-07-03 | NeuVT Limited | Endovascular occlusion device with hemodynamically enhanced sealing and anchoring |
| US10076399B2 (en) | 2013-09-13 | 2018-09-18 | Covidien Lp | Endovascular device engagement |
| WO2015153996A1 (en) | 2014-04-03 | 2015-10-08 | Micro Vention, Inc. | Embolic devices |
| US9713475B2 (en) | 2014-04-18 | 2017-07-25 | Covidien Lp | Embolic medical devices |
| US10092663B2 (en) | 2014-04-29 | 2018-10-09 | Terumo Corporation | Polymers |
| JP6599361B2 (en) | 2014-04-29 | 2019-10-30 | マイクロベンション インコーポレイテッド | Polymer containing an active agent |
| US9060777B1 (en) | 2014-05-28 | 2015-06-23 | Tw Medical Technologies, Llc | Vaso-occlusive devices and methods of use |
| CN106604696A (en) | 2014-05-28 | 2017-04-26 | 斯瑞克欧洲控股有限责任公司 | Vaso-occlusive devices and methods of use |
| US9814466B2 (en) | 2014-08-08 | 2017-11-14 | Covidien Lp | Electrolytic and mechanical detachment for implant delivery systems |
| US9808256B2 (en) | 2014-08-08 | 2017-11-07 | Covidien Lp | Electrolytic detachment elements for implant delivery systems |
| US9763814B2 (en) | 2014-10-24 | 2017-09-19 | Cook Medical Technologies Llc | Elongate medical device |
| CN104367370B (en) * | 2014-11-27 | 2017-01-11 | 上海交通大学医学院附属第九人民医院 | Oviduct plug and pushing device used in cooperation with oviduct plug |
| WO2016182949A1 (en) | 2015-05-08 | 2016-11-17 | Stryker European Holdings I, Llc | Vaso-occlusive devices |
| US9717503B2 (en) | 2015-05-11 | 2017-08-01 | Covidien Lp | Electrolytic detachment for implant delivery systems |
| WO2016201250A1 (en) | 2015-06-11 | 2016-12-15 | Microvention, Inc. | Expansile device for implantation |
| US10307168B2 (en) | 2015-08-07 | 2019-06-04 | Terumo Corporation | Complex coil and manufacturing techniques |
| US11090055B2 (en) | 2015-10-30 | 2021-08-17 | Incumedx Inc. | Devices and methods for delivering an implant to a vascular disorder |
| US10052108B2 (en) | 2015-10-30 | 2018-08-21 | Incumedx, Inc. | Devices and methods for delivering an implant to a vascular disorder |
| JP6836324B2 (en) | 2016-01-26 | 2021-02-24 | 株式会社シマノ | Electric reel |
| US11464948B2 (en) | 2016-02-16 | 2022-10-11 | Embolx, Inc. | Balloon catheters and methods of manufacture and use |
| US9550046B1 (en) | 2016-02-16 | 2017-01-24 | Embolx, Inc. | Balloon catheter and methods of fabrication and use |
| US10350382B1 (en) | 2018-06-08 | 2019-07-16 | Embolx, Inc. | High torque catheter and methods of manufacture |
| US10828037B2 (en) | 2016-06-27 | 2020-11-10 | Covidien Lp | Electrolytic detachment with fluid electrical connection |
| US10828039B2 (en) | 2016-06-27 | 2020-11-10 | Covidien Lp | Electrolytic detachment for implantable devices |
| US11051822B2 (en) | 2016-06-28 | 2021-07-06 | Covidien Lp | Implant detachment with thermal activation |
Family Cites Families (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4735201A (en) * | 1986-01-30 | 1988-04-05 | The Beth Israel Hospital Association | Optical fiber with detachable metallic tip for intravascular laser coagulation of arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| US4994069A (en) * | 1988-11-02 | 1991-02-19 | Target Therapeutics | Vaso-occlusion coil and method |
| US5354295A (en) * | 1990-03-13 | 1994-10-11 | Target Therapeutics, Inc. | In an endovascular electrolytically detachable wire and tip for the formation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| US5122136A (en) * | 1990-03-13 | 1992-06-16 | The Regents Of The University Of California | Endovascular electrolytically detachable guidewire tip for the electroformation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| JP3343684B2 (en) * | 1991-03-14 | 2002-11-11 | エトゥノール | Improved pulmonary embolism prevention filter and accessory positioning mounting kit |
| US5304194A (en) * | 1991-10-02 | 1994-04-19 | Target Therapeutics | Vasoocclusion coil with attached fibrous element(s) |
| EP0791333B1 (en) * | 1991-12-12 | 1999-12-01 | Target Therapeutics, Inc. | Detachable pusher-vasoocclusive coil assembly with interlocking coupling |
| US5234437A (en) * | 1991-12-12 | 1993-08-10 | Target Therapeutics, Inc. | Detachable pusher-vasoocclusion coil assembly with threaded coupling |
| US5261916A (en) * | 1991-12-12 | 1993-11-16 | Target Therapeutics | Detachable pusher-vasoocclusive coil assembly with interlocking ball and keyway coupling |
| US5509411A (en) * | 1993-01-29 | 1996-04-23 | Cardima, Inc. | Intravascular sensing device |
| US5250071A (en) * | 1992-09-22 | 1993-10-05 | Target Therapeutics, Inc. | Detachable embolic coil assembly using interlocking clasps and method of use |
| US5312415A (en) * | 1992-09-22 | 1994-05-17 | Target Therapeutics, Inc. | Assembly for placement of embolic coils using frictional placement |
| US5350397A (en) * | 1992-11-13 | 1994-09-27 | Target Therapeutics, Inc. | Axially detachable embolic coil assembly |
| US5382259A (en) * | 1992-10-26 | 1995-01-17 | Target Therapeutics, Inc. | Vasoocclusion coil with attached tubular woven or braided fibrous covering |
| US5382260A (en) * | 1992-10-30 | 1995-01-17 | Interventional Therapeutics Corp. | Embolization device and apparatus including an introducer cartridge and method for delivering the same |
| US5423829A (en) * | 1993-11-03 | 1995-06-13 | Target Therapeutics, Inc. | Electrolytically severable joint for endovascular embolic devices |
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- 1997-09-25 EP EP97307530A patent/EP0832606B1/en not_active Expired - Lifetime
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- 1997-09-26 JP JP09262332A patent/JP3102855B2/en not_active Expired - Fee Related
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| NO974436L (en) | 1998-03-27 |
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| EP0832606B1 (en) | 2003-06-04 |
| CA2216618A1 (en) | 1998-03-26 |
| US5690667A (en) | 1997-11-25 |
| DE69722545T2 (en) | 2004-04-22 |
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