fig1 illustrates a guide wire 10 embodying features of the invention that is adapted to be inserted into a patient &# 39 ; s body lumen , such as an artery or vein . the guide wire 10 comprises an elongated , relatively high strength proximal core section 11 , and a relatively short flexible distal core section 12 . the distal core portion 12 has at least one tapered section 21 which becomes smaller in the distal direction . a helical coil 22 is disposed about the distal core section 12 and is secured by its distal end to the distal end of shaping ribbon 23 by a mass of solder which forms rounded plug 24 when it solidifies . the proximal end of the helical coil 22 is secured to the distal core section 12 at a proximal location 25 and at intermediate location 26 by a suitable solder . the proximal end of the shaping ribbon 23 is secured to the distal core portion 12 at the same intermediate location 26 by the solder . preferably , the most distal section 27 of the helical coil 22 is made of radiopaque metal , such as platinum or platinum - nickel alloy , to facilitate the fluoroscopic observation thereof while it is disposed within a patient &# 39 ; s body . the most distal section 27 of the coil 22 should be stretched about 10 to about 30 % in length to provide increased flexibility . the most distal part 28 of the distal core section 12 is flattened into a rectangular cross - section and is preferably provided with a rounded tip 29 , e . g ., solder , to prevent the passage of the most distal part through the spacing between the stretched distal section 27 of the helical coil 22 . the exposed portion of the elongated proximal core section 11 should be provided with a coating 30 of lubricous material such as polytetrafluoroethylene ( sold under the trademark teflon ® by du pont , de nemours & amp ; co .) or other suitable lubricous coatings such as other fluoropolymers , hydrophilic coatings and polysiloxane coatings . the elongated proximal core section 11 of the guide wire 10 is generally about 130 to about 140 cm in length with an outer diameter of about 0 . 006 to 0 . 018 inch ( 0 . 15 - 0 . 45 mm ) for coronary use . larger diameter guide wires , e . g . up to 0 . 035 inch ( 0 . 89 mm ) or more may be employed in peripheral arteries and other body lumens . the lengths of the smaller diameter and tapered sections can range from about 1 to about 20 cm , depending upon the stiffness or flexibility desired in the final product . the helical coil 22 may be about 3 to about 45 cm in length , preferably about 5 to about 20 cm , has an outer diameter about the same size as the outer diameter of the elongated proximal core section 11 , and is made from wire about 0 . 001 to about 0 . 003 inch ( 0 . 025 - 0 . 08 mm ) in diameter typically about 0 . 002 inch ( 0 . 05 mm ). the shaping ribbon 23 and the flattened distal section 28 of distal core section 12 have generally rectangularly shaped transverse cross - sections which usually have dimensions of about 0 . 0005 to about 0 . 006 inch ( 0 . 013 - 0 . 152 mm ), preferably about 0 . 001 by 0 . 003 inch ( 0 . 025 - 0 . 076 mm ). the distal core section 12 is preferably made of nitinol , which is a psuedoelastic alloy material preferably consisting essentially of about 30 to about 52 % titanium and the balance nickel and optionally up to 10 % of one or more other alloying elements . the other alloying elements may be selected from the group consisting of iron , cobalt , vanadium , platinum , palladium and copper . the alloy can contain up to about 10 % copper and vanadium and up to 3 % of the other alloying elements . the addition of nickel above the equiatomic amounts with titanium and the other identified alloying elements increases the stress levels at which the stress induced austenite - to - martensite transformation occurs and ensures that the temperature at which the martensitic phase thermally transforms to the austenitic phase is well below human body temperature ( 37 degrees c .) so that austenite is the only temperature stable phase at body temperature . the excess nickel and additional alloying elements also help to provide an expanded strain range at very high stresses when the stress induced transformation of the austenitic phase to the martensitic phase occurs . moreover , it is known that heating nitinol excessively can change the pseudoelastic behavior , the martensite transitions temperatures , and even the shape memory . therefore , heat input into the nitinol should be carefully controlled . a presently preferred method for making the pseudoelastic distal core section is to cold work , preferably by drawing , a rod having a composition according to the relative proportions described above and then heat treating the cold worked product while it is under stress to impart a shape memory thereto . typical initial transverse dimensions of the rod are about 0 . 045 inch to about 0 . 25 inch . before drawing the solid rod , it is preferably annealed at a temperature of about 500 to about 750 degrees c ., typically about 650 degrees c ., for about 30 minutes in a protective atmosphere such as argon to relieve essentially all internal stresses . in this manner all of the specimens start the subsequent thermomechanical processing in essentially the same metallurgical condition so that products with consistent final properties are obtained . such treatment also provides the requisite ductility for effective cold working . the stress - relieved stock is cold worked by drawing in order to effect a reduction in the cross sectional area thereof of about 30 to about 70 %. the metal is drawn through one or more dies of appropriate inner diameter with a reduction per pass of about 10 % to 50 %. other forms of cold working can be employed such as swaging . following cold work , the drawn wire product is heat treated at a temperature between about 350 degrees c . and about 600 degrees c . for about 0 . 5 to about 60 minutes . preferably , the drawn wire product is simultaneously subjected to a longitudinal stress between about 5 % and about 50 %, preferably about 10 % to about 30 % of the tensile strength of the material ( as measured at room temperature ) in order to impart a straight “ memory ” to the metal and to ensure that any residual stresses therein are uniform . this memory imparting heat treatment also fixes the austenite - martensite transformation temperature for the cold worked metal . by developing a straight “ memory ” and maintaining uniform residual stresses in the pseudoelastic material , there is little or no tendency for a guide wire made of this material to whip when it is torqued within a patient &# 39 ; s blood vessel . the term “ whip ” refers to the sudden rotation of the distal tip of a guide wire when the proximal end of the guide wire is subjected to torque . an alternative method for imparting a straight memory to the cold worked material includes mechanically straightening the wire and then subjecting the straightened wire to a memory imparting heat treatment at a temperature of about 300 degrees to about 450 degrees c ., preferably about 330 degrees c . to about 400 degrees c . the latter treatment provides substantially improved tensile properties , but it is not very effective on materials which have been cold worked above 55 %, particularly above 60 %. materials produced in this manner exhibit stress - induced austenite to martensite phase transformation at very high levels of stress but the stress during the phase transformation is not nearly as constant as the previously discussed method . conventional mechanical straightening means can be used such as subjecting the material to sufficient longitudinal stress to straighten it . because of the extended strain range under stress - induced phase transformation which is characteristic of the pseudoelastic material described herein , a guide wire having a distal portion made at least in substantial part of such material can be readily advanced through tortuous arterial passageways . when the distal end of the guide wire engages the wall of a body lumen such as a blood vessel , it will pseudoelastically deform as the austenite transforms to martensite . upon the disengagement of the distal end of the guide wire from the vessel wall , the stress is reduced or eliminated from within the pseudoelastic portion of the guide wire and it recovers to its original shape , i . e ., the shape “ remembered ” which is preferably straight . the straight “ memory ” in conjunction with little or no nonuniform residual longitudinal stresses within the guide wire prevent whipping of the guide wire &# 39 ; s distal end when the guide wire is torqued from the proximal end thereof . moreover , due to the very high level of stress needed to transform the austenite phase to the martensite phase , there is little chance for permanent deformation of the guide wire or the guiding member when it is advanced through a patient &# 39 ; s artery . the present invention provides a guide wire which exhibits , at the distal portion , pseudoelastic characteristics to facilitate the advancement thereof in a body lumen . the distal guiding portion exhibits extensive , recoverable strain resulting from reversible , stress induced phase transformation of austenite to martensite at exceptionally high stress levels which greatly minimizes the risk of damage to arteries during the advancement therein . the high strength proximal portion of the guide wire generally is significantly stronger , i . e ., higher ultimate tensile strength , than the pseudoelastic distal portion . suitable high strength materials include 304 stainless steel which is a conventional material in guide wire construction . other high strength materials include nickel - cobalt - molybdenum - chromium alloys such as commercially available mp35n alloy . turning now to the connection between the stainless steel proximal portion 11 and the nitinol distal portion 12 of the guide wire , it has been found that connecting these two portions together by welding each to opposite ends of an intermediate transition piece formed from nickel achieves the desired connection without causing deficiencies in the strength and behavioral properties of the distal nitinol portion . while effectively unalloyed nickel is preferred for the transition piece , alloying the nickel with , for example , titanium , cobalt , copper or iron , to a degree which does not alter its ability to continuously form an essentially crack - free welded bond with the stainless steel proximal portion and nitinol distal portion , is permissible under alternative embodiments . in a preferred embodiment , exemplified in fig1 and 2 , a butt weld may be used at each end of the transition piece 30 which may be cylindrically shaped . the transition piece 30 advantageously may have an aspect ratio ( i . e ., ratio of length to diameter ) of between 0 . 5 and 3 , preferably greater than 1 . 0 . furthermore , as seen in fig2 b and 2c , the transition piece 30 may have a conical or a dome shaped end that is convex or concave . likewise , the interface surface of the proximal or distal portion 11 , 12 has a complementary mating shape . welding may be achieved by known methods of microwelding , such as friction welding , laser welding , electron beam welding , and plasma arc welding . examples of known welding methods are described in u . s . pat . no . 6 , 729 , 526 ( friction welding ), u . s . pat . no . 4 , 358 , 658 ( laser welding ), and u . s . pat . no . 5 , 951 , 886 ( electron beam welding ), the contents of which are incorporated herein by reference . in one preferred embodiment , friction welding is preferred as providing a high degree of precision and control . in another preferred embodiment , laser welding may be preferred as also providing a high degree of precision and control . in an alternative embodiment , exemplified in fig3 and 4 , transition piece 30 ′ may be shaped to contact the outer metal portions 11 , 12 at an angle oblique to the longitudinal guide wire axis between about 30 degrees and 60 degrees , preferably 45 degrees , to provide a larger area of contact for opposing welded surfaces . it will be appreciated that friction welding may not be possible under these conditions , but laser welding will be a preferred method , giving rise to a connection with greater surface contact between the welded parts than the previous embodiment , and thus greater tensile , compressive , and torsional resistance characteristics . in a further alternative embodiment , exemplified in fig5 and 6 , the transition piece 30 ″ may be shaped to fit between the outer metal portions 11 , 12 which are shaped to provide a connection substantially between a horizontal surface 32 of the proximal portion and an opposing horizontal surface 34 of the distal portion . this configuration may be adapted to have the advantage of providing an even larger area of contact between the juxtaposed parts than that of the embodiment of fig3 and 4 . a profile view of the transition piece 30 ″ gives the appearance of a zigzag shape . in yet a further alternative embodiment , exemplified in fig7 and 8 ( with similar advantages of the embodiment of fig5 and 6 ), the transition piece 30 ′″ may be shaped to connect the outer metal portions 11 , 12 which have in turn been shaped to provide a connection between a horizontal surface 36 of the proximal portion 11 and an adjacent non - opposing horizontal surface 38 of the distal portion 12 . a profile view of the transition piece 30 ′″ gives the appearance of a “ t ” shape . it will be appreciated that a combination of the various features of transition piece 30 , 30 ′, 30 ″ and 30 ′″ may be used . after the proximal and distal portions are thus connected , the guide wire may be cleaned in the vicinity of the connection by known means such as electropolishing , brushing , or grinding to remove any slag or minor rough spots . an advantageous characteristic arising from forming the transition piece 30 of nickel , or a mild alloy of nickel , is that , compared with vanadium which is known to be a successful transition piece for welding stainless steel to nitinol generally , nickel has a lower melting point than vanadium . thus , the microwelding process would tend to impart less heat to the distal portion of the guide wire than vanadium would require , and is therefore more suitable for microwelding as it is less likely to alter the beneficial characteristics of the nitinol alloy ( such as the amount of pseudo - elasticity and the phase transition temperatures ) in the process of welding . another advantageous feature of nickel is that it has a higher coefficient of thermal expansion than vanadium , and thus is better matched with the higher coefficient of thermal expansion of the stainless steel proximal portion , and of the distal nitinol portion . accordingly , during heating or cooling of the weld in this case , less volumetric expansion or contraction differential may occur at the boundaries between the transition piece and the proximal and distal portions , and consequently , there is less tendency for cracking or locked - in stresses to form at the boundaries . the resulting guide wire presents a uniform outer profile , allowing free movement of catheter elements along the guide wire during operation . in the context of microwelding workpieces as small as those of an intraluminal guide wire ( i . e ., less than 0 . 040 inches ), the solution of interposing a welded transition piece formed essentially of nickel between a stainless steel portion and a nitinol portion achieves adequate strength and flexibility . while a particular form of the invention has been illustrated and described , it will also be apparent to those skilled in the art that various modifications can be made without departing from the spirit and scope of the invention . accordingly , it is not intended that the invention be limited except by the appended claims .
an intravascular guide wire having two core materials joined together without the use of a connector tube or sleeve , the core materials being stainless steel and psuedoelastic metal alloy , nitinol . the core materials are joined to each other through an intermediate transition piece made essentially of nickel , which is welded on either side to the two core materials . in alternative embodiments , the intermediate piece may have different shapes to provide different strengths and advantages as may be required .