angioplasty catheter systems and procedures enable operators to perform life - saving treatments with minimal tissue trauma experienced by the patient . referring now to fig1 an angioplasty catheter 10 of the &# 34 ; over the wire &# 34 ; design having a radially expandable balloon 12 is shown positioned within a branch blood vessel 14 . from the point of entry , typically an incision made at 16 , to the eventual destination 18 , the catheter must traverse a winding , branch laden path . as a result , the catheter must rely on a relatively flexible guide wire to establish the path for the catheter to track . referring now to fig2 and 3 , a guide wire in accordance with a first embodiment of the present invention , generally designated 20 , provides variable stiffness capability in vivo and includes a flexible member 30 moveable relative to a stiffener 40 that longitudinally extends along respective guide wire segments defining a proximal shaft 22 , an intermediate section 24 , and a distal portion 26 . the flexible member 30 comprises a core wire formed of a relatively flexible strand of stainless steel measuring about 180 centimeters and having a relatively constant diameter over a majority of its length . typically , the diameter ranges from about 0 . 005 inches to 0 . 01 inches , depending upon the application involved . respective primary and secondary tapers 32 and 34 are formed in the core wire along the intermediate section to narrow the core wire and provide added flexibility . a distal end 36 of the core wire terminates in a bonded distal joint 38 that connects the intermediate section 24 the distal portion 26 of the guide wire . with continuing reference to fig2 and 3 , the stiffener 40 comprises a formed hypotube that coaxially extends longitudinally along the core wire 30 in slidable relationship therewith . the hypotube is formed with a relatively stiff shaft section 42 that narrows down , at 44 , to define a shoulder 46 for mounting one end of an intermediate spring 48 . the other end of the spring projects axially beyond the distal joint 38 and defines an inner spring 54 that terminates at a distal tip 58 . the narrowed section of the hypotube provides somewhat more flexibility than the stiff shaft section and tapers radially inwardly at 50 to form a restricted mouth 52 for complementally engaging the core wire secondary taper 34 . the mouth and the secondary taper cooperate to form an axially and radially inhibiting friction fit . the proximal shaft 22 and the intermediate section 24 together comprise various lengths of the core wire 30 and the hypotube 40 . however , for convention purposes , the intermediate spring 48 typically defines the guide wire intermediate section . thus , under this convention , the proximal shaft 22 extends from the proximal end of the guide wire ( not shown ), to the annular shoulder 46 formed in the slidable hypotube 40 . further referring to fig2 the distal portion 26 extends axially from the distal joint 38 and includes respective inner and outer coil springs 54 and 56 disposed concentrically and interposed between the distal joint 38 and the distal tip 58 . the tip typically retains a pre - formed &# 34 ; j &# 34 ; shape ( not shown ) to urge the guide wire in desired directions and thereby assist in steering the catheter during insertion through the vasculature . assembly of the guide wire 20 is well within the level of skill in the art , and generally includes first sliding the core wire 30 through the length of the hypotube 40 until the restricted mouth 34 frictionally engages the secondary taper 34 . the intermediate spring 48 is then run over the uncovered portion of the core wire projecting outwardly from the distal tip of the hypotube and attached to the annular shoulder 46 with a suitable adhesive . the distal joint 38 is then formed at the tip of the core wire 30 to confine the intermediate spring therearound with a globule of solder material or the like . with the inner spring 54 projecting axially from the intermediate spring , the outer spring 56 is slid coaxially over the inner spring and then bonded to the distal joint with adhesive . next , the opposite ends of the springs are capped by mounting the hemispherical tip 58 . following assembly , the guide wire is typically packaged separately in a sterile container for use in an angioplasty catheter system . referring now to fig1 and 3 , during operation , the guide wire 20 is typically first removed from its sterile packaging and inserted into the vascular system through the small external incision 16 . initial advancement of the guide wire through the body requires a relatively high degree of flexibility at the distal portion 26 of the guide wire , with a moderate level of flexibility at the intermediate section 24 . to maximize available flexibility at the distal portion , the hypotube 40 conveniently frictionally locks to the core wire 30 by sliding the hypotube rearwardly to engage the complementally formed mouth 52 and secondary taper 34 . locking of the core wire 30 to the hypotube 40 also serves to maximize the transmission of torque from the proximal end 22 of the guide wire to the intermediate section 24 by integrating the core wire and hypotube into a relatively large diameter rod , rather than a substantially thin wire . those skilled in the art will appreciate this feature to substantially assist the operator in steering the guide wire 20 through the vasculature . for example , as shown in fig1 a typical path for the guide wire 20 to traverse often includes sharp turns such as at 60 , and branch points leading to a plurality of branch paths , such as at 62 and 64 . the guide wire may be conveniently steered and threaded along the path by rotating the entire assembly to orient the pre - formed &# 34 ; j &# 34 ; ( not shown ) such that the hook points in a desired direction . however , as the blood vessels become more constrained , rotation of the guide wire along the 180 centimeter length becomes more difficult , and even stops altogether unless the proximal , intermediate and distal portions have a relatively high torsional stiffness . under such circumstances , the operator merely locks the hypotube 40 and the core wire 30 together to achieve the added torsional stiffness necessary to permit rotation of the guide wire in constrained areas . once the guide wire 20 is successfully threaded in position , the operator may then choose to stiffen the intermediate section 24 by sliding the hypotube 40 distally to provide axial support near the treatment area . advancement of the hypotube distally along the core wire , as shown in fig3 compresses the intermediate spring while bringing more of the relatively stiff shaft section of the hypotube into the intermediate section of the guide wire . the net result is a cooperative stiffening of the intermediate section by the interaction of the hypotube with the core wire . with the added axial support , the balloon or stent catheter 10 may track the guide wire 20 and treat the location without undesirable overflexing at the intermediate section of the guide wire . following the treatment , the hypotube may be shifted back to its initially locked position to enable swift withdrawal of the guide wire from the body . referring now to fig4 and 5 , a guide wire in accordance with a second embodiment of the present invention , generally designated 70 , is formed substantially similar to the first embodiment albeit with a modified core wire 72 construction . the core wire includes a sawtooth wave - shaped diametrically offset portion 74 disposed between a secondary barrel 73 and a secondary taper 75 . the offset portion provides a friction fit when engaged with an internal radial surface 76 in a hypotube 80 . in operation , the guide wire 70 functions in much the same manner as the first embodiment , but provides a locking friction fit over a greater range of hypotube positions . fig4 illustrates a locked position , while the stiffening action of the hypotube shifted axially is shown in fig5 . referring now to fig6 and 7 , in yet another embodiment , a guide wire 81 is formed substantially similar to the aforedescribed embodiments albeit with a modified core wire / hypotube construction . the guide wire includes a core wire 82 formed with a polygonal cross - section , such as a hexagonal or pentagonal shape . an inner surface 84 of a hypotube 86 is complementally formed with the same polygonal shape to axially receive the formed core wire . operation of the modified core wire / hypotube embodiment is also similar to the previously described embodiments . however , unlike the prior constructions , which included a selectively engageable locking mechanism to effect enhanced torsional stiffness , the modified construction provides continuous torsional support . during positional maneuvering of the guide wire , rotation of the hypotube 86 rotates the inner wire 82 due to the complementally formed polygonal surfaces thereby transmitting any applied torque from the proximal end to the tip and directing the j - shaped tip into the desired branch of the artery . with reference to fig8 and 9 , a guide wire in accordance with a fourth embodiment of the present invention , and generally designated 100 , includes a stiffener 110 slidably received within a closed ended flexible member 120 that longitudinally extends along respective segments defining a proximal shaft 102 , an intermediate section 104 , and a distal portion 106 . the stiffener 110 comprises a core wire formed of an elongated thin rod of tungsten / stainless steel alloy having a diameter within the range of 0 . 004 inches to 0 . 009 inches and a length of approximately 180 centimeters . unlike the first and second embodiments , the core wire diameter remains constant with the distal tip truncated in a flat engagement end 112 . further referring to fig8 the flexible member 120 comprises a formed hypotube including a relatively flexible tubular body formed with an interior blind bore 122 having a constant internal diameter to slidably receive the core wire 110 and a distal wall 124 to serve as a stop . the exterior of the hypotube includes a major diameter 126 extending most of the hypotube length . the major diameter narrows at 128 along a secondary taper 130 and ends in a secondary barrel 132 . the secondary barrel extends longitudinally to 134 where it begins to fall off in a primary taper 136 that extends to a primary barrel 138 . the end of the hypotube is swaged down into a tapered section 140 that bonds to a distal joint 142 . with further reference to fig8 an intermediate spring 144 telescopically receives the hypotube 120 and bonds to the secondary taper 130 through the use of a suitable adhesive that forms an adhesive joint 146 . the opposite end of the spring connects to the distal joint 142 . unlike the first and second embodiments , the intermediate spring 144 lies mounted in an axially fixed position . the distal portion 106 is formed substantially similar to the first and second embodiments . an inner spring 148 is formed integrally with the intermediate spring and projects axially distally . the inner spring tapers radially inwardly and then forms a constant diameter in an axially expanded configuration to provide a larger pitch . an outer spring 150 coaxially confines the inner spring and bonds with the inner spring to the distal point 142 . a hemispherical cap 152 bonds to the ends of the springs . assembly of the guide wire 100 involves first inserting the intermediate spring 144 over the distal end of the hypotube 120 and bonding one end of the spring to the secondary taper at 154 . the other end of the spring is then bonded or soldered to the distal joint 142 , along with the distal end of the hypotube itself , and the respective inner and outer springs 148 and 150 . the cap 152 is then attached to the opposite end of the springs and pre - formed with the springs to take on a &# 34 ; j &# 34 ;- shape ( not shown ). the core wire 110 is then inserted through the length of the hypotube . referring to fig8 and 9 , during operation , the guide wire 100 is initially inserted into the vasculature with the core wire 110 somewhat retracted from the end of the hypotube 120 to maximize the flexibility of the assembly during advancement along winding vessels . in relatively constricted areas where turns must be artfully negotiated , the operator merely rotates the hypotube shaft to effect a corresponding rotation at the distal portion 106 , thereby re - orienting the distal &# 34 ; j &# 34 ;, and urging the guide wire along another direction . because of the relatively large diameter of the hypotube 120 , the transmission of rotation of the assembly from the proximal end to the intermediate section is substantially unaffected . once positioned at the treatment site , the guide wire stiffness may be increased by conveniently sliding the core wire 110 through the hypotube bore 122 toward the formed stop 124 . advancement of the core wire distally results in a cooperation between the core wire and the hypotube to impart a varying stiffness corresponding to the depth of insertion of the core wire through the hypotube bore 122 . depending upon the application , the guide wire will reflect a level of stiffness necessary to properly support a balloon or stent catheter . when the procedure is completed , the core wire may be removed to restore flexibility to the guide wire so that it may be quickly removed . those skilled in the art will appreciate the many benefits and advantages afforded by the present invention . of significant importance is the controllable axial stiffness feature requiring merely relative axial displacement of the core wire with respect to the hypotube to vary the flexibility of the guide wire in vivo . this feature eliminates the need to effect any exchange in hardware preliminary to the actual stent delivery or balloon expansion step . the invention also offers an important advantage in allowing the operator to adjust the torsional stiffness during operation merely by locking the hypotube and core wire together ( as in the first and second embodiments ), or through the inherent nature of the hypotube design itself ( third embodiment ). such an advantage permits reliable rotational steering of the guide wire through the vascular system with minimal torsional interference caused by constricted blood vessels and the like . while the invention has been particularly shown and described with reference to the preferred embodiments thereof , it will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the spirit and scope of the invention .
an angioplasty guidewire includes a proximal shaft and an intermediate section extending from the shaft to a distal joint and having a stiffener and a flexible member . the stiffener and the flexible member are disposed in coaxial slidable relationship and operable , as the stiffener and flexible member undergo relative axial shifting , to cooperatively impart a variable stiffening force on the intermediate section . a flexible distal tip mounts to the end of the intermediate section and projects axially therefrom .