Guide wire device including a solderable linear elastic nickel-titanium distal end section and methods of preparation therefor

Patent metadata

Field	Value
Publication number	US-9724494-B2
Application number	US-201113172278-A
Country	US
Kind code	B2
Filing date	Jun 29, 2011
Priority date	Jun 29, 2011
Publication date	Aug 8, 2017
Grant date	Aug 8, 2017

Abstract

Shapeable guide wire devices and methods for their manufacture. Guide wire devices include an elongate shaft member having a shapeable distal end section that is formed from a linear pseudoelastic nickel-titanium (Ni—Ti) alloy that has linear pseudoelastic behavior without a phase transformation or onset of stress-induced martensite. Linear pseudoelastic Ni—Ti alloy, which is distinct from non-linear pseudoelastic (i.e., superelastic) Ni—Ti alloy, is highly durable, corrosion resistant, and has high stiffness. The shapeable distal end section is shapeable by a user to facilitate guiding the guide wire through tortuous anatomy. In addition, linear pseudoelastic Ni—Ti alloy is more durable tip material than other shapeable tip materials such as stainless steel.

First claim

What is claimed is:

1. A shapeable guide wire device configured to allow a practitioner to shape a distal end to a desired shape for tracking through a patient's vasculature, the shapeable guide wire comprising:
an elongate shaft member that includes a proximal end section and a flattened distal end section formed of a linear pseudoelastic nickel titanium alloy such that the flattened distal end section does not exhibit a phase transformation or onset of stress-induced martensite as the flattened distal end section is stressed, the flattened distal end section having a metallic material applied over the linear pseudoelastic nickel titanium alloy in a pre-cold work state of the elongate shaft member, the flattened distal end section, with the metallic material applied thereto, having a constant cross-sectional dimension and a length from 2 cm to 10 cm and being a practitioner-shapeable distal end section as a result of the flattened distal end section being formed from the linear pseudoelastic nickel titanium alloy;
wherein the practitioner-shapeable distal end section has a yield stress from about 150 ksi to about 200 ksi;
a helical coil section disposed about at least the practitioner-shapeable distal end section; and
an atraumatic cap section attached to the helical coil section and the metallic material of the practitioner-shapeable distal end section, wherein the distal end section alone extends along the length of the helical coil to the atraumatic cap.

2. The shapeable guide wire device of claim 1 , wherein the elongate shaft member comprises stainless steel, a superelastic nickel-titanium alloy, or a combination thereof.

3. The shapeable guide wire device of claim 1 , wherein the practitioner-shapeable distal end section exhibits 20% to 90% cold work.

4. The shapeable guide wire device of claim 1 , the practitioner-shapeable distal end section exhibits 40% to 50% cold work.

5. The shapeable guide wire device of claim 1 , wherein the atraumatic cap section comprises a cap of solder and wherein the solder material includes a eutectic alloy.

6. The shapeable guide wire device of claim 5 , wherein the eutectic alloy is selected from the group consisting of a gold-tin solder, a gold-indium solder, a gold-germanium solder, a silver-tin solder, and a silver-gold-tin solder.

7. The shapeable guide wire device of claim 5 , wherein the gold-tin solder includes about 80 weight % (wt %) gold and about 20 wt % tin.

8. The shapeable guide wire device of claim 1 , wherein the atraumatic cap section comprises a cap of solder soldered to the helical coil section and the practitioner-shapeable distal end section.

9. A method for fabricating a guide wire device, comprising:
fabricating an elongate shaft member that includes a proximal end section and a distal end section, wherein the distal end section is formed of a distal nickel-titanium alloy member having a first cross-sectional dimension;
applying a first layer of solder material by vapor deposition to at least a portion of the distal end section;
following applying the soldering material, cold working at least a portion of the distal end section having the solder material applied thereto, wherein the cold working yields a distal practitioner-shapeable end section having a second cross-sectional dimension and in which the nickel-titanium alloy in this cold worked region has linear pseudoelastic deformation behavior without a phase transformation or onset of stress-induced martensite; and
soldering the distal shapeable section and a helical coil section disposed about the distal practitioner-shapeable section to an atraumatic cap without substantial loss of the linear pseudoelasticity of the distal practitioner-shapeable section, the distal end section, including the distal practitioner-shapeable end section, alone extending through the helical coil section to the atraumatic cap;
wherein the distal practitioner-shapeable end section has a yield stress from about 150 ksi to about 200 ksi.

10. The method of claim 9 , wherein the cold working includes at least one of high force flattening, stamping, rolling, or calendaring.

11. The method of claim 9 , wherein the distal practitioner-shapeable section comprises a cold-worked microstructure that includes 40% to 50% cold work.

12. The method of claim 9 , wherein the distal practitioner-shapeable section comprises a cold-worked microstructure that includes about 45% cold work.

13. The method of claim 9 , wherein the first cross-sectional dimension is about 0.08 mm round and the second cross-sectional dimension is in a range of 0.065 mm to 0.008 mm.

14. The method of claim 9 , wherein the first cross-sectional dimension is about 0.08 mm round and the second cross-sectional dimension is about 0.045 mm.

15. The method of claim 9 , further comprising applying a second coating of solder to at least a portion of the distal end section, over the first layer of solder material, the second coating of solder being a separately applied coating relative to the atraumatic cap.

16. The method of claim 9 , wherein the cold-worked distal practitioner-shapeable end section is in a martensitic phase.

17. The method of claim 16 , wherein the martensitic phase is substantially preserved in forming the soldered joint.

18. The method of claim 16 , wherein the martensitic phase is stabilized by the cold working.

19. A method for fabricating a guide wire device having a shapeable distal end section, the method comprising:
providing an elongate shaft member that includes a proximal end section and a distal end section, wherein the distal end section is formed of a nickel-titanium alloy member;
grinding at least a portion of the distal end section to a first cross-sectional dimension;
cold working by flattening a first time at least a distal portion of the distal end section;
ultrasonically cleaning at least the distal end section;
dipping at least a portion of the distal end section into a bath of a molten solder material, wherein the bath of molten solder material includes an upper layer of a molten metal hydroxide and a lower layer of the molten solder material;
following dipping at least a portion of the distal end section into a bath of molten solder material, cold working a second time by flattening at least a distal portion of the distal end section having the solder material applied thereto, the cold working exhibiting 40% to 50% cold work wherein a first cross-sectional dimension is about 0.08 mm round and a second cross-sectional dimension is about 0.045 mm, wherein the cold working yields a distal practitioner-shapeable end section in which the nickel-titanium alloy in this cold worked region has linear pseudoelastic deformation behavior such that it is selectively shapeable;
ultrasonically cleaning at least the distal end section;
disposing a helical coil section about the distal practitioner-shapeable section; and
soldering the distal practitioner-shapeable section and the helical coil section to an atraumatic cap without substantial loss of the linear pseudoelasticity of the nickel-titanium alloy in the distal practitioner-shapeable section, the distal end section, including the distal practitioner-shapeable end section, alone extending through the helical coil section to the atraumatic cap;
wherein the distal practitioner-shapeable end section has a yield stress from about 150 ksi to about 200 ksi.

20. The method of claim 19 , wherein dipping at least a portion of the distal end section into a bath comprises dipping at least a por

Assignees

• Purtzer Raleigh A
• Abbott Cardiovascular Systems Inc

Inventors

• Purtzer Raleigh A

Classifications

• C22F1/183

  of titanium or alloys based thereon · CPC title

• C22F1/10

  of nickel or cobalt or alloys based thereon · CPC title

• C22F1/006

  Resulting in heat recoverable alloys with a memory effect · CPC title

• C21D2211/001

  Austenite · CPC title

• C21D2201/01

  Shape memory effect · CPC title