as discussed herein , implementations of an enhanced implantable system and method include use of one or more pseudoelastic and / or superelastic materials ( referred to herein as “ p / s elastic ”) such as p / s elastic metal alloys , such as nitinol , and / or p / s elastic polymers to provide at least a portion of the associated support structure for the implantable antenna . in implementations , the support structure has the general shape of the associated antenna either by one or more portions as integrated support structures being directly incorporated into the antenna structure typically as a tubular support structure and / or portions serving as a backbone support structure with a shape similar to the supported antenna components such as including inductive ( h - field ) and e - field antenna implementations discussed herein . use of p / s elastic material in the antenna support structure provides greater implantation adaptability and accommodation for the enhanced implantable antenna compared with conventional approaches . the p / s elastic materials used can have elastic response over large strains . for instance , when mechanically loaded , p / s elastic materials can deform reversibly even under strains , of up to approximately 6 % to 10 % so that the antenna structure will return to a desired shape after undergoing large strain levels . this large reversible elastic deformation capability provides relatively high flexibility to accommodate minimally invasive insertion into the body , and other implantation scenarios . furthermore , pseudoelastic materials exhibit a stress plateau at larger strains , which is desirable for accommodating motion within the body and for minimizing the stress on tissues . fig1 through 6 illustrate various cross sectional views of antenna implementations that can be used with the implant versions shown in fig7 through 11 . a first implementation 100 of the enhanced implantable antenna system incorporating tubular support is sectionally shown in fig1 to include a coaxial set 102 of an electrically conductive core 104 filling a tubular support structure 106 , which is further encased by an external electrical insulator 108 . versions of the coaxial set 102 that use a drawn filled tube ( dft ) wire of p / s elastic material , such as nitinol , for the tubular support structure 106 can serve both a support role and an antenna role for the enhanced implantable antenna system . given the various biological environments ( such as in and around vicinities of the heart ) of the enhanced implantable antenna system , the p / s elastic material used for the tubular support structure 106 and other support structures discussed herein has long fatigue life ( such as 1 , 000 , 000 cycles , 10 , 000 , 0001 cycles , 100 , 000 , 000 cycles , and / or 400 , 000 , 000 cycles for temperature ranges such as of at least between 33 degrees celsius to 43 degrees celsius or such as of at least between 0 degrees celsius to 100 degrees celsius )) to exist in areas such as inside of the heart . some versions of the enhanced implantable antenna system also use p / s elastic materials with high elasticity : some having an elastic strain level of approximately 3 % or more and others having an elastic strain level of approximately 6 % or more for temperature ranges such as of at least between 33 degrees celsius to 43 degrees celsius or such as of at least between 0 degrees celsius to 100 degrees celsius to provide flexibility to be collapsed or compressed to allow for temporary enclosure by delivery mechanisms , such as a catheter , a cannula , or other mechanical tubular structure of a delivery mechanism before being released to expand into an uncompressed state to be located in a vascular structure , other endoluminal tubular structure or biological tubular structure . since nitinol is superelastic , it can be strained up to an elastic limit of about 6 % without permanent deformation . some p / s elastic materials , such as nitinol , have an additional advantage in that they have shape memory properties , and can be “ shape - set ” to a desired geometry . in the case of nitinol , the shape setting process requires holding the wireform in a desired geometry while undergoing a heat treatment at a temperature of approximately 500 degrees celsius . due to the high shape - setting temperature , a nitinol or nitinol dft antenna member requires shape setting prior to applying polymeric electrical insulation such as could be used for the external insulator 108 . several different insulation techniques are possible , including vapor deposition ( e . g ., parylene ), dip or spray coating ( various polymers , either in the melt phase or prior to cross - linking ), casting , injection molding , or by swelling a polymeric extrusion and sliding the shape - set wires into position . the latter technique is most easily accomplished using a silicone extrusion , which can be swelled in a liquid such as pentane , hexane , heptane , xylene , or a low molecular weight alcohol . the presence of the solvent in the silicone makes it particularly lubricious , allowing insertion of the wires with minimal force . like other p / s elastic materials , nitinol and nitinol dft wires include another advantageous aspect . nitinol has two crystalline states : martensite at low temperatures and austenite at higher temperatures . the transition temperature may be tailored by adjusting the metallurgical composition and processing that the material undergoes during manufacturing , to produce transition temperatures at , above , or below room temperature . in medical applications , the transition temperature can thus be set between room temperature (˜ 20 ° c .) and body temperature ( 37 ° c . ), so that a device transitions from its martensitic phase to its austenitic phase as it is introduced into the body . only the austenitic phase is superelastic , whereas the martensitic phase is quite plastic . in some implementations , p / s elastic material , such as nitinol , can be processed as follows : shape - set the subject member , such as the coaxial set 102 and / or the tubular support structure 106 , to the desired shape at approximately 500 ° c . cool the subject member to transition it into its martensitic phase straighten ( or otherwise shape ) the subject member to facilitate application of the insulating material , such as the external insulator 108 apply insulating material , such as the external insulator 108 to the subject member implant final assembly steps can be completed with the subject member in either phase as required by other considerations . a second implementation 110 of the enhanced implantable antenna system is sectionally shown in fig2 to include two of the coaxial sets 102 of the conductive core 104 and the tubular support structure 106 both encased in an external insulator 112 . a third implementation 114 of the enhanced implantable antenna system is sectionally shown in fig3 to include four of the coaxial sets 102 of the conductive core 104 and the tubular support structure 106 all encased in an external insulator 116 . any quantity of the coaxial set 102 can be put together in this fashion . a fourth implementation 120 of the enhanced implantable antenna system is sectionally shown in fig4 to include three of the coaxial sets 102 of the conductive core 104 and the tubular support structure 106 and insulated conductors 122 having an elongated conductive member 124 encased by an insulator 126 . the three coaxial sets 102 and the four insulated conductors 122 are further encased in an insulator 127 . the three coaxial sets 102 and the four insulated conductors 122 are shown in a symmetrical configuration , but other symmetrical or asymmetrical configurations can also be implemented in various other numbers of the coaxial sets and of the insulated conductors . whereas other implementations can be made , given the implementation depicted in fig4 , one to three of the coaxial sets 102 and one to four of the insulated conductors 122 may be connected electrically in series or parallel to form an antenna configuration . each of the elongated conductive members 124 in some implementations are solid conductors as the conductive core 104 as shown in fig4 a . in other implementations , the elongated conductive members 124 are each a bundle of stranded conductors 124 b such as shown in fig4 b . each of the stranded conductors 124 b can be solid core conductors such as smaller diameter versions of the conductive core 104 as shown in fig4 c or can be smaller diameter versions of the coaxial set 102 as shown in fig4 d or another type of drawn filled tube ( dft ) wire or drawn brazed strand ( dbs ) wire with a conductive core . to maintain superelastic properties of the stranded wire , one or more of the strands would be chosen to contain nitinol , either in solid , dft , or other form . in other implementations , each of the elongated conductive members 124 can be versions of the coaxial set 102 as shown in fig4 e . in alternative implementations , as shown in fig4 f , each of the elongated conductive members 124 can be from a drawn brazed strand ( dbs ) 128 with strands 128 a made from a fatigue - resistant alloy , and braze 128 b and center core 128 c made from a conductive material such as silver or other highly conductive material . further implementations include the elongated conductive member 124 as a coaxial set 129 , as shown in fig4 g , with a tubular support structure 129 a ( such as a dft ) made from material other than the p / s elastic material ( such as mp35n or other fatigue resistant alloy ). the tubular structure 128 a of the coaxial set 128 can be filled with the conductive core 104 . other implementations of the stranded conductor 124 b can be made with versions of the coaxial set 129 as shown in fig4 h . since nitinol and mp35n are far more resistive than either silver or copper , in some implementations with portions of the tubular support structure 106 being made from nitinol or the tubular support structure 129 a made from mp35n and the conductive core 104 being made from a metal such as silver or copper , most of the electrical current will flow through the conductive core rather than the tubular support structure . although highly fatigue - resistant composite wires such as mp35n dft and dbs , when filled with a highly conductive metal such as silver , exhibit excellent electrical conductivity , they do not exhibit the superelastic properties or the shape memory properties of nitinol . nitinol dft , mp35n dft , and dbs composite wires are commercially available with core cross - sections ranging from about 15 % to 41 % of the total area . even with a 15 % cross - section dedicated for the conductive core 104 , with many of the constructions , a majority of electrical current would flow through a low resistivity conductive core , such as made from silver , copper , or gold . in some applications , a material for the conductive core 104 is chosen due to its enhanced radiopaque properties which result from the atomic number and mass density of the core metal . for example , gold offers higher radiopacity than silver or copper , while retaining relatively low resistivity . a fifth implementation 130 of the enhanced implantable antenna system is sectionally shown in fig5 as having a backbone support structure 132 including a p / s elastic core 134 , encased in a sleeve 136 . in some implementations the p / s elastic core 134 is made from shape - set nitinol and the sleeve 136 is made from a polymer such as ptfe , fep , pfa , etfe , pvdf , peek , ldpe , hdpe , polyurethane , silicone , or blends or alloys of these materials . the fifth implementation 130 further includes three of the insulated conductors 122 all of which are encased along with the backbone support structure 132 in an electrical insulator 140 . each of the three insulated conductors 122 each occupy a corner position of a triangular configuration of the insulator 140 in one implementation as shown in fig5 , and has a circular sectional shape of the insulator 140 in another implementation as shown in fig5 a . in some implementations the backbone support structure 132 is used solely for structural support to provide shape enhancement whereas in other implementations , in addition to structural support , the backbone support structure also provides antenna functionality . in both fig5 and 5a , the insulated conductors 122 are drawn as ellipses to illustrate that they can be helically wound around the backbone support structure 132 . the form of the helix can range from zero to a plurality of turns per unit length , as required for a specific application . a sixth implementation 150 of the enhanced implantable antenna system is sectionally shown in fig6 as having the backbone support structure 132 surrounded by eight of the insulated conductors 122 and all encased in an insulator 152 . fig7 - 11 show representative versions of implants that incorporate the enhanced implantable antenna system including the implementations depicted above . in fig1 - 3 and 7 - 11 , the implantable antenna system may be used for inbound power delivery to the implant , inbound signal communication to the implant , and / or outbound signal communication to an external system . in fig7 - 9 , implants with versions of the implantable antenna system with inductive loop antennas are shown , which can have one or multiple turns of any one of the implementations described above . a first implant version 160 is shown in fig7 to include an inductive h - field loop antenna 162 coupled with an electronic enclosure 164 on a first side 166 and a second side 168 of the electronic enclosure . the first implant version 160 is shown in fig7 as being in an uncompressed state having a measurement of zu along a first dimension and is shown in fig7 a as being in a compressed state having a measurement of zc along the first dimension to be fitted into a delivery tubular structure 169 having an interior 169 a with an internal diameter , d . in some implementations , the ratio between zu and zc is at least 3 : 1 and in other implementations at least 5 : 1 . the loop antenna 162 includes one or more electrical conductors and one or more mechanical elements such as found in the depicted implementations described above or with other implementations using aspects of the enhanced implantable antenna system . a second implant version 170 is shown in fig8 to include two of the inductive ( h - field ) loop antennas 162 both coupled to an electronic enclosure 172 on a first side 174 and a second side 176 . the second implant version 170 is shown in fig8 as being in an uncompressed state having a measurement of zu along a first dimension and is shown in fig8 a as being in a compressed state having a measurement of zc along the first dimension to be fitted into a delivery tubular structure 179 having an interior 179 a with an internal diameter , d . in some implementations , the ratio between zu and zc is at least 3 : 1 and in other implementations at least 5 : 1 . the two loop antennas 162 provide additional area for transmitting or receiving magnetic field signals , and they provide an alternate mechanical shape for anchoring the device in an anatomic location . having two of the loop antennas 162 to the second implant version 170 for inbound power , inbound communications , or outbound communications provide added power and / or signal strength for inbound power or communication and added signal strength and / or field shaping for outbound communication . these loop antennas need not reside in the same plane . a third implant version 180 is shown in fig9 to include a first inductive ( h - field ) loop antenna 182 ( having a first portion 182 a and a second portion 182 b ) and a second inductive ( h - field ) loop antenna 184 having a first portion 184 a and a second portion 184 b ) both coupled to a first electronic enclosure 186 ( having a first side 186 a and a second side 186 b ) and a second electronic enclosure 188 ( having a first side 188 a and a second side 188 b ). the third implant version 180 is shown in fig9 as being in an uncompressed state having a measurement of zu along a first dimension and is shown in fig9 a as being in a compressed state having a measurement of zc along the first dimension to be fitted into a delivery tubular structure 189 having an interior 189 a with an internal diameter , d . in some implementations , the ratio between zu and zc is at least 3 : 1 and in other implementations at least 5 : 1 . the first portion 182 a of the first loop antenna 182 and the first portion 184 a of the second loop antenna 184 both extend between the first side 186 a of the first electronic enclosure 186 and the first side 188 a of the second electronic enclosure 188 . the second portion 182 b of the first loop antenna 182 and the second portion 184 b of the second loop antenna 184 both extend between the second side 186 b of the first electronic enclosure 186 and the second side 188 b of the second electronic enclosure 188 . the third implant version 180 has advantages associated with two loop antennas similar to the second implant version 170 and provides an alternative shape for anchoring in an anatomic location . the third implant version 180 also has the additional space for electronic components associated with a second electronic enclosure , namely , the second electronic enclosure 188 spaced apart from the first electronic enclosure 186 . a fourth implant version 200 as shown in fig1 has an electrical e - field antenna 202 coupled to an electronic enclosure 204 . the e - field antenna 202 has an elongated member 206 coupled to the electronic enclosure 204 and extending therefrom . coupled with the elongated member 206 as also included with the e - field antenna 202 , is a helical coil section 208 , which can be threaded into tissue to provide a mechanical anchor for the fourth implant version 200 . the fourth implant version 200 is shown in fig1 as being in an uncompressed state with the helical coil section 208 having a measurement of zu along a first dimension and is shown in fig1 a as being in a compressed state with the helical coil section having a measurement of zc along the first dimension to be fitted into the delivery tubular structure 209 having an interior 209 a with an internal diameter , d . in some implementations , the ratio between zu and zc is at least 3 : 1 and in other implementations at least 5 : 1 . the electronic enclosure 204 of the fourth implant version 200 can be either in electrical or capacitive contact with surrounding tissue and would act as a local electrical ground reference . given this arrangement , an e - field could be produced ( for outbound signaling ) or sensed ( for inbound power delivery or signaling ) between the electronic enclosure 204 and the e - field antenna 202 . a fifth implant version 210 as shown in fig1 has a first electrical e - field antenna 202 and a second electrical e - field antenna 204 both coupled to either end of an electronic enclosure 206 . the first e - field antenna 202 and the second e - field antenna 204 are both configured as straight sections which can be inserted into soft tissue to provide a mechanical anchor . in the fifth implant version 210 , the electronic enclosure 206 can be insulated from adjacent areas of tissue having received implantation of the fifth implant version . an e - field could be produced ( for outbound signaling ) or sensed ( for inbound power delivery or signaling ) between the first e - field antenna 202 and the second e - field antenna 204 as a dipole antenna . fig1 a shows the fifth implant being inserted into a tubular structure 219 . from the foregoing it will be appreciated that , although specific embodiments of the invention have been described herein for purposes of illustration , various modifications may be made without deviating from the spirit and scope of the invention . accordingly , the invention is not limited except as by the appended aspects . 1 . for implantation through a tubular structure into a biological structure , a system comprising : an antenna electrically coupled to the electronic device , at least a portion of the antenna being helical , the helical portion of the antenna having a uncompressed state with a measurement , zu , along a first dimension and a compressed state with a measurement , zc , along the first dimension . 2 . the system of aspect 1 wherein the helical antenna portion includes : an electrically conductive structure coupled with the p / s elastic structure ; and 3 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is a p / s elastic tubular structure . 4 . the helical antenna portion of aspect 3 wherein the electrically conductive structure fills the p / s elastic tubular structure . 5 . the helical antenna portion of aspect 3 wherein the p / s elastic structure is a drawn filled tube . 6 . the helical antenna portion of aspect 5 wherein the electrically conductive structure serves as filling material for the p / s elastic structure as the drawn filled tube . 7 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is made from a material that is pseudoelastic in a temperature range of at least 33 degrees celsius to 43 degrees celsius . 8 . the helical antenna portion of aspect 7 wherein the p / s elastic structure is made from a material that is pseudoelastic in a temperature range of at least 0 degrees celsius to 100 degrees celsius . 9 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is made from a material that is superelastic in a temperature range of at least 33 degrees celsius to 43 degrees celsius . 10 . the helical antenna portion of aspect 9 wherein the p / s elastic structure is made from a material that is superelastic in a temperature range of at least 0 degrees celsius to 100 degrees celsius . 11 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is made from a nickel - titanium alloy . 12 . the helical antenna portion of aspect 11 wherein the p / s elastic structure is made from nitinol . 13 . the helical antenna portion of aspect 12 wherein the electrically conductive has a higher electrical conductivity than nitinol . 14 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is made from a metal . 15 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is made from a polymer . 16 . the helical antenna portion of aspect 2 wherein the electrically conductive structure is of at least one of the following materials : silver , copper , gold , aluminum , iridium , brass , nickel , platinum . 17 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is in an austenitic phase in at least a temperature range between 33 degrees celsius and 43 degrees celsius . 18 . the helical antenna portion of aspect 2 wherein the p / s elastic structure is shaped set with shape memory properties to maintain a desired shape in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 19 . the helical antenna portion of aspect 2 wherein the p / s elastic structure has an elastic strain range of at least 3 % in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 20 . the helical antenna portion of aspect 19 wherein the p / s elastic structure has an elastic strain range of at least 6 % in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 21 . the helical antenna portion of aspect 19 wherein the p / s elastic structure has an elastic strain range of at least 3 % in a temperature range of at least between 0 degrees celsius and 100 degrees celsius . 22 . the helical antenna portion of aspect 19 wherein the p / s elastic structure has an elastic strain range of at least 6 % in a temperature range of at least between 0 degrees celsius and 100 degrees celsius . 23 . the helical antenna portion of aspect 1 wherein the ratio of zu to zc is at least 3 : 1 . 24 . the helical antenna portion of aspect 23 wherein the ratio of zu to zc is at least 5 : 1 . 25 . the helical antenna portion of aspect 1 wherein the measurement of zc is an internal diameter of a catheter . 26 . the helical antenna portion of aspect 1 wherein the measurement of zc is an internal diameter of a cannula . 27 . the helical antenna portion of aspect 26 wherein the helical antenna portion has a fatigue life of at least 1 , 000 , 000 cycles in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 28 . the helical antenna portion of aspect 27 wherein the helical antenna portion has a fatigue life of at least 10 , 000 , 000 cycles in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 29 . the helical antenna portion of aspect 28 wherein the helical antenna portion has a fatigue life of at least 100 , 000 , 000 cycles in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 30 . the helical antenna portion of aspect 29 wherein the helical antenna portion has a fatigue life of at least 400 , 000 , 000 cycles in a temperature range of at least between 33 degrees celsius and 43 degrees celsius . 31 . the helical antenna portion of aspect 26 wherein the helical antenna portion is shaped as a loop in a temperature range of at least between 33 degrees celsius to 43 degrees celsius . 32 . the helical antenna portion of aspect 1 wherein the helical antenna portion is configured to receive electric fields for the electronic device . 33 . the helical antenna portion of aspect 1 wherein the helical antenna portion is configured to transmit electric fields for the electronic device . 34 . the helical antenna portion of aspect 33 wherein the biological structure is a blood vessel and the helical antenna portion is shaped and sized to be received by the blood vessel . 35 . the helical antenna portion of aspect 33 wherein the p / s elastic structure extends along a central axis of the helical antenna portion . 36 . the helical antenna portion of aspect 35 wherein electrically conductive structure extends along the central axis of the helical antenna portion . 37 . the helical antenna portion of aspect 36 wherein the electrically conductive structure fills the p / s elastic structure along the central axis of the helical antenna portion . 38 . the helical antenna portion of aspect 35 wherein the electrically conductive structure spirals around the p / s elastic structure . 39 . the helical antenna portion of aspect 33 wherein the electrically conductive structure extends along the central axis of the helical antenna portion and the p / s elastic structure extends along another axis parallel with the central axis . 40 . the helical antenna portion of aspect 33 wherein the electrically conductive structure is of a solid construction . 41 . the helical antenna portion of aspect 33 wherein the electrically conductive structure is of a stranded construction . 42 . the helical antenna portion of aspect 33 wherein the p / s elastic structure is of a solid construction . 43 . the helical antenna portion of aspect 33 wherein the p / s elastic structure is of a stranded construction . 44 . the helical antenna portion of aspect 33 wherein the p / s elastic structure is of a drawn brazed strand construction . 45 . the helical antenna portion of aspect 33 wherein the p / s elastic structure is configured to be electrically coupled to an electronic device . 46 . the helical antenna portion of aspect 33 wherein the electrically conductive structure is configured to be electrically coupled to an electronic device . 47 . the helical antenna portion of aspect 46 wherein the p / s elastic structure is configured to be electrically insulated rather than being electrically coupled to the electronic device . 48 . for implantation through a tubular structure into a biological structure , an antenna configured to electrically couple to an electronic device , at least a portion of the antenna being helical , the helical portion of the antenna having a uncompressed state with a measurement , zu , along a first dimension and a compressed state with a measurement , zc , along the first dimension , the helical antenna portion including : an electrically conductive structure coupled with the p / s elastic structure ; and an electrical insulator coupled with at least one of the p / s elastic structures . 49 . the helical antenna portion of aspect 48 further including a plurality of electrically conductive structures wherein each of the plurality of p / s elastic structures is tubular , each of the electrically conductive structures filling a different one of the p / s elastic structures . 50 . the helical antenna portion of aspect 49 further including a plurality of electrical insulators , each electrical insulator of the plurality covering a different one of the plurality of the p / s elastic structures and the electrical insulator coupled with the plurality of the p / s elastic structures through the electrical insulator . 51 . the helical antenna portion of aspect 48 wherein each of the plurality of p / s elastic structures is coupled to the electrical insulator , further including a plurality of electrically conductive structures coupled to the p / s elastic structures through the electrical insulator . 52 . the helical antenna portion of aspect 51 further including a plurality of electrical insulators each covering a different one of the plurality of the electrically conductive structures . 53 . the helical antenna portion of aspect 48 wherein the electrically conductive structure is configured for electrical coupling with an electronic device . 54 . the helical antenna portion of aspect 53 wherein the electrically conductive structure is electrically isolated from the plurality of p / s elastic structures . 55 . the helical antenna portion of aspect 54 wherein the electrically conductive structure is electrically isolated from the plurality of p / s elastic structures through the electrical insulator . 56 . for implantation through a tubular structure into a biological structure , an antenna configured to electrically couple to an electronic device , at least a portion of the antenna being helical , the helical portion of the antenna having a uncompressed state with a measurement , zu , along a first dimension and a compressed state with a measurement , zc , along the first dimension , the helical antenna portion including : a plurality of electrically conductive structures coupled with the p / s elastic structure ; and 57 . the helical antenna portion of aspect 56 , further including a plurality of p / s elastic structures wherein one of the plurality of electrically conductive structures is coupled to the p / s elastic structure and the others of the plurality of electrically conductive structures are each directly coupled to a different one of the plurality of p / s elastic structures . 58 . the helical antenna portion of aspect 57 , further including a plurality of electrical insulators , each electrical insulator of the plurality covering a different one of the plurality of the electrically conductive structures . 59 . the helical antenna portion of aspect 56 further including a plurality of p / s elastic structures coupled to the electrically conductive structures through the electrical insulator . 60 . the helical antenna portion of aspect 56 further including a plurality of electrical insulators each covering a different one of the plurality of the electrically conductive structures . 61 . the helical antenna portion of aspect 56 wherein each of the electrically conductive structures are configured for electrical coupling with an electronic device . 62 . the helical antenna portion of aspect 56 wherein each of the electrically conductive structures are electrically isolated from the plurality of p / s elastic structures . 63 . the helical antenna portion of aspect 56 wherein each of the electrically conductive structures are electrically isolated from the plurality of p / s elastic structures through the electrical insulator . 64 . the helical antenna portion of aspect 56 wherein each of the electrically conductive structures spiral around the p / s elastic structure .
as described herein vascular anchoring systems are used to position an implant in a vascular area such as a bifurcated vasculature with relatively high fluid flow , for instance , in an area of a pulmonary artery with associated left and right pulmonary arteries . implementations include an anchoring trunk member having a first anchoring trunk section and a second anchoring trunk section . further implementations include a first anchoring branch member extending from the anchoring trunk member . still further implementations include a second anchoring branch member extending from the anchoring trunk member .