as noted above , the guglielmi et al . system for deploying an implant into the human body uses a core wire , an electrolytic sacrificial joint , and the implant to be deployed . a power supply is needed to provide power for electrolysis of the joint . the core wire is typically insulated on its outer surface from near the proximal end of the wire and along the wire to the electrolytic sacrificial joint . the implant typically forms a portion of the circuit through the body . this invention substantially removes the implant itself from that circuit thereby apparently focusing the current flow at the electrolytic joint where it is needed for electrolysis . [ 0035 ] fig1 shows a system for introducing and deploying the implant made according to the invention . the system ( 100 ) includes a catheter ( 102 ) which is made up of an elongate tubular member , typically made from a polymeric material and often reinforced with a coil or braid to provide strength or obviate kinking propensities . catheter ( 102 ) is shown with a pair of radiopaque markers ( 106 ). the radiopaque markers ( 106 ) allow visualization of the distal end ( 104 ) of the catheter so to compare it with the coincidence of the implant . catheter ( 102 ) is also shown with a proximal fitting ( 108 ) for introduction of dyes or treatment materials . within the lumen of catheter ( 102 ) is a core wire ( 110 ) extending both proximally of catheter ( 102 ) and distally . on the distal end of core wire ( 110 ) may be seen the electrolytic joint ( 112 ) and the implant ( 114 ). in this instance , implant ( 114 ) is shown to be a helically wound vaso - occlusive coil . generally , all of core wire ( 110 ) is electrically insulated from a point near the proximal end of core wire ( 110 ) continuously to electrolytically severable joint ( 112 ). electrolytically severable joint ( 112 ) is bare and is relatively more susceptible to electrolysis in an ionic solution such as blood or most other bodily fluids than is the implant ( 114 ). the most proximal end of core wire ( 110 ) is also left bare so that power supply ( 116 ) may be attached . the other pole of the power supply ( 116 ) is typically attached to a patch ( 118 ). the patch is placed on the skin to complete the circuit from the power supply ( 116 ), through the core wire ( 110 ), through electrolytic joint ( 112 ), through the ionic solution in the body , and back to a patch ( 118 ) to the power supply ( 116 ). other return routes may be used as the designer sees fit . central to this invention is electrical isolation of implant ( 114 ) from core wire ( 110 ) and electrolytically severable joint ( 112 ). without wishing to be bound by theory , it is believed that isolation of the implant ( 114 ) prevents or lessens current flow through the implant ( 114 ) itself and concentrates the current flow through the electrolytic joint ( 112 ). [ 0038 ] fig2 shows a close - up of the more distal portion of one variation of the invention . this variation includes the core wire ( 110 ) and the attached implant ( 120 ). typically , core wire ( 110 ) will be conductive but covered with a insulative layer ( 111 ) both proximal and distal of electrolytically severable joint ( 112 ). the interior of core wire ( 110 ) is physically attached to implant ( 120 ). in this variation of the invention , implant ( 120 ) is a helically wound coil . in this invention , a highly resistive or insulative layer or member electrically isolates implant ( 120 ) from core wire ( 110 ). in this variation of the invention , the insulating layer ( 111 ) on the core wire ( 110 ) is simply continued to the end of the core wire ( 110 ). an optional bushing ( 114 ) is placed on the core wire ( 110 ) to further separate it from implant ( 120 ). optional bushing ( 114 ) may be of any suitable material since it operates merely as a spacer . insulating layer ( 111 ) may be polytetrafluoroethylene ( e . g ., teflon ), polyparaxylylene ( e . g ., parylene ), polyethyleneterephthalate ( pet ), polybutyleneterephthalate ( pbt ), cyanoacrylate adhesives , or other suitable insulating layer , but preferably is polymeric and most preferably is pet . the coil making up this variation ( and other coil - based variations ) of the invention is generally of a diameter in the range of 0 . 025 inches and 0 . 006 inches . wire of such diameter is wound into a primary form having a diameter of between 0 . 003 and 0 . 025 inches . for most neurovascular indications , the preferable primary coil diameter is preferably between 0 . 008 and 0 . 018 inches . the axial length of the primary coil will usually fall in the range of 0 . 5 to 100 cm , more usually 2 . 0 to 40 cm . depending upon usage , the coil may well have 10 - 75 turns per centimeter , preferably 10 - 40 turns per centimeter . all of the dimensions here are provided only as guidelines and are not critical to the invention . however , only dimensions suitable for use in occluding sites within the human body are included in the scope of this invention . [ 0042 ] fig3 shows a close - up of another variation of the invention including the more distal portion of the core wire ( 110 ) and the attached implant ( 120 ). in this variation of the invention , implant ( 120 ) is a helically wound coil having a stretchresistant member ( 134 ) through its center lumen . the anti - stretch member ( 134 ) may be of any suitable material , e . g ., metallic wire or polymeric threads . preferred are polymeric threads comprised of a member selected from the group consisting of polyethylene , polypropylene , polyamides , and polyethyleneterephthalate although almost any polymeric material which is formable into a fiber is quite suitable . the stretch - resistant member is simply designed to prevent the coil ( 120 ) from stretching in the event that core wire ( 110 ) must be withdrawn or repositioned to change the position of the implant ( 120 ). the stretch - resistant member ( 134 ) is attached to an interior anchor coil ( 136 ) having a distal hook ( 138 ) to which the stretch - resistant member ( 134 ) is attached . an optional bushing ( 140 ) is present and attached to the metallic center of the core wire ( 110 ). in this variation of the invention , either or both of the optional bushing ( 140 ) or interior anchor coil ( 136 ) may be of an oxide - forming material such as tantalum and the like . we have found that when tantalum or other such refractory forming materials are subjected to welding operations as may be found when assembling this device , an apparently oxidic , but highly electrically resistive layer is formed at the junction of the tantalum and its neighbor . [ 0044 ] fig4 shows another variation ( 150 ) of the inventive implant assembly . in this variation , bushing ( 152 ) is formed of an oxidic or insulative - forming material and is included to form such a resistive layer during operations to weld the metallic center ( 154 ) to bushing ( 152 ). [ 0045 ] fig5 shows another variation ( 158 ) of the inventive implant assembly . in this variation , the implant ( 120 ) is attached to the core wire ( 110 ) and at the same time is electrically insulated from the metallic center ( 154 ) of core wire ( 110 ) by the use of a glue or thermopolymer ( 156 ) made from a suitable polymer , e . g ., a thermoplastic , preferably comprising a member selected from the group consisting of polyethylene , polypropylene , polyamides , and polyethyleneterephthalate . an “ oxide forming material ” or “ insulator - forming material ” as those terms are used herein are materials which , under the imposition of an appropriate electrical current or other such excitation , will form an insulating , preferably oxide , layer . one such material is the metal tantalum and certain of its alloys . other insulation forming materials or oxide forming materials include zirconium . although the use of solid insulation forming material is shown in fig3 and 4 , the use of an insulation forming material in a layer is also contemplated . such a layer may be plated , sputtered , painted , heat shrunk , glued , or melted onto the appropriate part . [ 0048 ] fig6 shows another variation of the invention , in this case using a polymeric insert between core wire ( 110 ) and helical deployment coil ( 120 ). electrolytically severable joint ( 112 ) is also shown . the polymeric insert ( 121 ) typically includes a radiopaque marker coil ( 123 ) and is simply slid over the distal tip of core wire ( 110 ) and into the lumen of helical coil ( 120 ). once so assembled , this assemblage is heat - treated to cause the various portions to adhere to each other . as is the case with any of the other variations shown herein , it may be desirable to place circumferential ribs on the distal tip of core wire ( 110 ) to provide a more suitable bond for the polymeric insert ( 121 ). care must be taken , of course , to ensure that polymeric plug ( 121 ) contains no materials ( e . g ., dyes or opacifiers ) which would enhance the conductivity of the plastic . it is the task of polymeric insert ( 121 ) to insulate core wire ( 110 ) from deployable helical coil ( 120 ) so the electrolytic joint ( 112 ) is easily and readily detached . it should be noted , that although the radiopaque coil ( 123 ) is highly desirable , in this invention , it is completely optional . [ 0049 ] fig6 shows still another variation of the invention . this variation is a similar concept both to the polymeric plug variation shown in fig8 and to the variation shown in fig3 involving a stretch - resistant member . in this variation , polymeric plug ( 125 ) is again slipped over the distal portion of core wire ( 110 ) and into the proximal portion of helical coil ( 120 ). the assembled joint is heated so to allow whatever thermoplastic that may be in polymeric insert ( 125 ) to flow and secure the detachable implant ( 120 ) to the core wire . electrolytically severable joint ( 112 ) is also shown . the major difference between this variation and others seen before is in the presence of coil ( 127 ) fixedly attached to stretch - resistant member ( 129 ). of particular interest is the fact that coil ( 127 ) is soldered or preferably welded to detachable helical coil ( 120 ) in the region ( 131 ). coil ( 127 ) should be made from a material similar to that of helical detachable coil ( 120 ) to prevent any untoward — happenings during the severance of electrolytic joint ( 112 ) by provision of voltage couples or the like . [ 0052 ] fig8 shows still another variation of the invention of the invention in which a polymeric plug is used to separate the core wire ( 103 ) from the deployable implant ( 107 ). incidentally , core wire ( 103 ) is shown to have an external marker ( 105 ) at its proximal end . core wire ( 103 ) additionally has , adjacent detachment region ( 109 ), a surface ( 111 ) which is cut on a bias or at an angle to the axis of core wire ( 103 ). as is discussed in a number of prior patents assigned to target therapeutics incorporated , this biased surface ( 111 ) enhances the physician &# 39 ; s ability to detach the implantable device ( 107 ) from core wire ( 103 ) once electrolysis or electro - erosion is completed . this surface ( 111 ) is formed by use of a plug ( 113 ) which is typically polymeric in nature . a series of coils ( 115 ) and ( 117 ) are also shown in this variation . coils ( 115 ) and ( 117 ) are typically produced of radiopaque material . they are positioned to allow easy visualization of the detachment region ( 109 ). the depiction found in fig8 further has a shrink - wrap coating ( 119 ) on the exterior of the device proximal of the detachment area ( 109 ). in this instance , the proximal end of the implant ( 107 ), distal of the detachment zone ( 109 ) is constructed of a number of polymeric portions which allow for easy and practical assembly of the overall device . in particular , radiopaque coil ( 121 ) is surrounded by polymeric region ( 123 ). it is often the case that assembling the device shown in fig8 the bare distal end of core wire ( 103 ) will first be wrapped with coil ( 121 ) and then the so - wrapped coil ( 121 ) will then be dipped in molten polymeric material to form the polymeric region ( 123 ). a polymeric plug , typically thermoplastic ( 125 ) is also inserted into the proximal end of implant ( 107 ). a polymeric coating , typically thermoplastic and typically a shrink - wrap is then placed over the two polymeric masses ( 123 ) and ( 125 ). upon application of appropriate heat , outer covering ( 127 ) serves to attach the distal end of core wire ( 103 ) with the proximal end of implant ( 107 ). in many instances , the polymers used variously in region ( 123 ), region ( 125 ), and covering ( 127 ) are the same . desirably , they are miscible with each other upon application of appropriate heat . it is also appropriate that they merely bind to each other in a well - defined way . this variation of the device is quite easy to assemble and the radiopaque coil ( 123 ) gives the physician - user a well - defined end point for introduction of the implant ( 107 ) into the aneurysm or other cavity . [ 0055 ] fig9 shows a variation of the invention similar to that found in fig8 except that it shows the use of a strain resistant vaso - occlusive device . for purposes of this description all of the core wire ( 103 ) proximal of detachment zone ( 109 ) is the same as is shown in fig8 . similarly , the distal end of coil wire ( 103 ) includes a radiopaque coil ( 121 ) initially covered by a polymeric covering or region ( 123 ). in this instance , the polymeric region ( 131 ) placed within the proximal end of vasoocclusive implant ( 107 ) includes a coil ( 133 ) having a distal loop ( 135 ) thereon . that distal loop is , in turn , attached to a stretch - resistant member ( 137 ) of the type discussed at length above with regard to fig3 . again , this device may be assembled using a thermoplastic or shrink - wrap covering ( 139 ) placed exteriorly about polymeric region ( 123 ) and the proximal end of implant ( 107 ). [ 0056 ] fig1 and 11 show still another variation of the insulative joint . in particular , fig1 shows a implant ( 141 ) located distally of the region ( 109 ). in this instance , the distal end of the core wire has a radiopaque coil ( 143 ) wrapped around . central to this variation of the invention is the presence of an anchoring member ( 145 ). anchoring member ( 145 ) typically has a small loop ( 147 ) allowing for connection of the stretch - resistant member ( 149 ). it is desirable to include a polymeric region ( 151 ) distally of anchoring member ( 145 ). polymeric region ( 151 ) may be placed in the implant ( 141 ) in such a way that it makes the stretch - resistant member ( 149 ) adhere well to the anchor member ( 145 ). anchor member ( 145 ) should have a diameter which is larger than that of the interior of the implant ( 141 ) so that should the distal end of implant ( 141 ) be pulled strongly , the end of anchor member ( 145 ) not be able to pass through the lumen of implant member ( 141 ). again , as with the variations shown in fig8 and 9 , the exterior of the joint region shown in fig1 may be all assembled using a polymeric tubing , preferably thermoplastic , which adheres to and joins all of the noted pertinent parts together . [ 0057 ] fig1 shows a similar variation of the anchor member ( 153 ) but is somewhat different in that the loop ( 155 ) for attaching to the strain resisting member ( 149 ) is larger and there is no polymeric region ( 151 ) as was shown in fig1 . the variation shown in fig8 and 9 and especially those shown in fig1 and ii are particularly useful when utilizing the insulating joint of this invention in combination with a very flexible vaso - occlusive coil as the implant . such a highly flexible vaso - occlusive coil is described in u . s . pat . nos . 5 , 669 , 931 ( kupiecki et al .) and 5 , 690 , 666 ( bernstein et al .). the entirety of these patents is hereby incorporated by reference . although the preferred variation of the invention is that found in the figures discussed above wherein a helical coil implant is fixably attached distally of electrolytically severable joint ( 112 ), other implants are suitable . for instance , fig1 shows another variation of the inventive device ( 160 ) in which the implant is a vaso - occlusive braid ( 162 ), either woven or unwoven . the electrolytically severable joint ( 164 ) is shown proximally of vaso - occlusive braid ( 162 ). in this variation , the core wire is insulated with a tubular member ( 168 ) and a bushing ( 170 ). a stabilizing coil ( 172 ) is also depicted on the distal end of core wire ( 166 ). bushing ( 170 ) and covering ( 168 ) serve to electrically insulate core wire ( 166 ) from the surrounding ionic fluid . these coverings along with the isolating joint ( not shown in cross section in this figure ) found on vaso - occlusive woven braid ( 162 ) apparently focus the electrolysis process on the electrolytically severable joint ( 164 ). when the implant is a vaso - occlusive device , the shape of the device may be any of a number of suitable overall shapes to promote occlusion of the selected interior body space . in particular , when the implant is a helical coil , many shapes are known for treatment of particular abnormalities . fig1 and 14 show useful devices for treatment of arterio - venous malformations ( avm ) and aneurysms . specifically , fig1 shows a vaso - occlusive coil ( 180 ) which has a secondary conical shape . a “ secondary ” shape is meant to include any form in which a wire is first formed into a first helical shape and that first helical shape is wound into a second shape which is , possibly , but not necessarily , helical . secondary forms include generally spherical , ovoid , elongated , and any other form into which the device will “ self - form ” upon relaxation either within a body open region or simply outside the delivery catheter . as was noted above , vaso - occlusive devices are introduced through a catheter . pushing the vaso - occlusive device through the catheter uses that first linear configuration which approximates the shape of the interior of the catheter . secondary shape such as shown in fig1 and 14 are formed when the vaso - occlusive device is allowed to exit the distal end of the catheter . the secondary shape of the vaso - occlusive device ( 180 ) shown in fig1 is , as noted just above , conical in form . [ 0061 ] fig1 shows a variation ( 182 ) of the inventive device in which two sections of the vaso - occlusive device have different secondary diameters . each of the vaso - occlusive devices described herein may also have attached fibrous materials to increase their thrombogenicity . [ 0063 ] fig1 shows a variation ( 190 ) of the inventive device in which the implant is a stent ( 192 ). core ( 194 ) is also is shown with an electrolytically erodable joint ( 196 ). the stent show in fig1 is a variation of a self expanding stent typically made of a super - elastic alloy material , typically a nickel - titanium alloy ( e . g ., nitinol ), that is well known in the art . the device has a zig - zag pattern of a metallic wire which is maintained in the noted and secondary form by a filament ( 198 ) which is woven through the bends of the stent to maintain the secondary shape . the primary shape is simply the shape shown but with a significantly lower diameter . the form of the stent is not important to the invention but is only illustrative of the form an implant may take [ 0065 ] fig1 shows the expanded form of an implant ( 200 ) which may be used as a vena cava filter . vena cava filters are well known in the art and are used to prevent the flow of blood clots distally in the vasculature . these blood clots would eventually be the site of occlusive strokes in the brain if allowed to travel distally . in any event , implant ( 200 ) shows the vena cava filter member ( 202 ), the electrolytically severable joint ( 204 ) and the push wire or core wire ( 206 ). [ 0066 ] fig1 a and 17b show placement of the inventive devices , specifically the vaso - occlusive variations of the invention , within the human body . fig1 a shows the placement within a vessel ( 200 ) with a tip of catheter ( 202 ) placed near aneurysm neck ( 204 ). the aneurysm itself is nominated ( 206 ). vaso - occlusive device ( 208 ) is fed into aneurysm ( 206 ) at least until the sacrificial link or joint ( 210 ) ( hidden within catheter ( 202 ) at this step ) is exposed beyond the distal tip of catheter ( 202 ). a positive electric current of approximately 0 . 01 - 2 milliamps at 0 . 1 - 6 volts as applied to core wire ( 212 ). an embolic mass is then formed within aneurysm ( 206 ). the negative pole ( 214 ) of power supply ( 216 ) is typically placed in electrical contact with . the skin so to complete the circuit . the vaso - occlusive device ( 208 ) is detached from core wire ( 212 ) by electrolytic disintegration of sacrificial link ( 210 ). after sacrificial link ( 210 ) is at least mostly dissolved by electrolytic action , typically in less than two minutes and most often in less than one minute , the core wire ( 212 ), catheter ( 202 ), are removed from vessel ( 200 ) leaving aneurysm ( 206 ) occluded as represented by occlusion ( 218 ) in fig1 b . this procedure is typically practiced under fluoroscopic control with local or general anesthesia . a transfemoral catheter may be used to treat cerebral aneurysm and is usually introduced at the groin . when the vaso - occlusive device ( 208 ) is isolated by a highly resistive material as is contemplated this invention , it is not affected by electrolysis . when the core wire ( 212 ) and the pertinent portions of the supporting coils at the distal tip of the core wire ( when utilized ) are adequately coated with insulating coverings , only the exposed portion of the sacrificial link ( 210 ) is affected by the electrolysis . we compared detachment times for commercially available guglielmi detachable coils ( gdc ) with those for a variation of the invention similar to that shown in fig3 . we constructed three sets of ten implant assemblies . the first set ( fig1 ) were commercial gdc assemblies as modified below . the second set ( fig1 ) had tantalum interior anchor coils (( 136 ) in fig3 ) and a distal hook ( 138 ) to which the stretch - resistant member ( 134 ) was attached . the third set ( fig1 ) were similar to those described in regard to fig6 incorporating a pet insulator between the detachable coil and the electrolytic joint . the implants on each were platinum coils . in the second set , the platinum bushing ( 140 ) was included and attached to the metallic center of the core wire ( 110 ). the assembly of tantalum interior anchor coil , platinum bushing , and core wire ( 110 ) was welded together . to exaggerate and lengthen the detachment times for each set , as would be the case when an implant is inserted into an aneurysm already having a number of platinum coils with vestigal remaining stainless steel stubs remaining from prior detachments and having electrical contact with those coils , an additional stainless steel wire of about one inch length was added to the detachable coils . the resulting detachment times for the coils were increased by as much as ten - fold as is sometimes seen clinically . each of the comparative commercial gdc &# 39 ; s and the inventive variations were placed in a saline bath and subjected to a constant amperage of 1 ma and a resulting voltage of between 1 . 5 and 2 . 0 volts . the time for electrolytic erosion of the joint was measured . as shown in fig1 , the average time for detachment of the commercial gdc coil was 454 . 9 seconds . as shown in fig1 , the average time for detachment of the inventive variation gdc coil using tantalum insulator coils was 125 . 1 seconds . as shown in fig2 , the average time for detachment of the inventive variation gdc coil using a pet insulator sock was 38 seconds . many alterations and modifications may be made by those having ordinary skill in this art without departing from the spirit and scope of the invention . the illustrative embodiments have been used only for the purposes of clarity and should not be taken as limiting the invention as defined by the following claims .
this is an implant for placement in the human body and an assembly for so placing that implant . most desirably , it is an implant for use in the vasculature of the human body and is used to occlude some space in that vasculature as a portion of a treatment regimen . the implant itself is preferably a component of a deployment device using an electrolytically severable joint . the implant is electrically isolated from the electrolytically severable joint by a highly resistive or insulative layer . such isolation and minimization of the conductive pathway from the placement apparatus to the body &# 39 ; s fluids appears to enhance the susceptibility of the electrolytic joint to quick erosion and detachment of the implant from the deployment media . although the implant itself is preferably a vaso - occlusive device , it may instead be a stent , a vena cava filter , or other implant which may be installed in this manner .