turning now to fig1 a through 2 and 13 through 15 , various embodiments of the modular needle apparatus are illustrated . in each of these embodiments , the modular needle apparatus includes a hollow delivery needle 10 having a proximal port 15 opening into a lumen 20 which extends through the delivery needle 10 to its distal end . the lumen 20 is sized to accommodate alternately a biopsy needle 30 and an ablation needle 35 . both the biopsy needle 30 and the ablation needle 35 are longer than the delivery needle 10 such that when either is inserted into the proximal port 15 , a distal projection may extend from the distal end of the delivery needle 10 . in this fashion , the biopsy needle 30 may obtain a tissue sample . in addition , the distal projection of the ablation needle 35 forms a microwave antenna 40 for performing tissue ablation . in certain embodiments , illustrated in fig1 a through 1 g , inserting the ablation needle 35 into the lumen 20 of the delivery needle 10 forms a coaxial transmission line 50 which supplies power to the microwave antenna 40 . in such embodiments , the delivery needle 10 comprises a conductive material that functions as the outer conductor 16 of the coaxial transmission line 50 , while a center conductor 55 of the ablation needle 35 circumferentially surrounded by dielectric material 60 acts as the center conductor and dielectric of the coaxial transmission line 50 . delivery needle 10 preferably further comprises a jacket 17 of electrically and / or thermally insulating material such as parylene or teflon ® which at least partially surrounds outer conductor 16 ( shown in fig1 a ). delivery needle 10 may have a flat or a sharpened distal end . as used herein , a “ flat ” distal end indicates a bevel of 90 ° as described in andriole et al ., biopsy needle characteristics assessed in the laboratory , radiology 148 : 659 - 662 , september 1983 , the contents of which are hereby incorporated by reference . in an alternate embodiment , illustrated in fig1 through 15 , the microwave antenna 40 couples to a transmission line 61 contained entirely within the ablation needle 35 such that the delivery needle 10 has no electrical transmission function , although it may provide additional shielding and / or act as an insulator . thus , in these embodiments , the delivery needle 10 and the ablation needle 35 do not couple together to create the coaxial transmission line 50 of fig1 d . it is to be noted that by coupling the delivery needle 10 with the ablation needle 35 to create the coaxial transmission line 50 feeding the microwave antenna 40 , the largest diameter that must enter the tissue may be kept very small , preferably of 17 gauge or higher , and more preferably 18 gauge or higher . as used herein , “ gauge ” shall refer to the outer diameter of a needle unless otherwise indicated . for such embodiments , the ablation needle 35 comprises a center conductor 55 circumferentially surrounded by a dielectric material 60 . the dielectric material 60 may comprise a ceramic material , a fluoropolymer such as polytetrafluoroethylene ( ptfe ) or expanded ptfe , polyethylene ( pe ), silicone or other suitable materials . the dielectric material 60 is sized to fill the lumen 20 of the delivery needle 35 . the diameter of the center conductor 55 and the inner diameter of the outer conductor 16 are chosen according to the equation : where z is the characteristic impedance , ε is the dielectric constant of the dielectric material 60 , d is the inner diameter of outer conductor 16 , and d is the diameter of center conductor 55 . typically , z is chosen to be 50 ω . the value of ε is typically between 1 and 10 , for example , the ε of ptfe is 2 . 1 . in addition , to promote efficient conduction along the coaxial transmission line 50 , the inner surface of outer conductor 16 of the delivery needle 10 may be coated with a layer of very conductive metal such as ag , au , cu or al preferably to a thickness of at least the skin depth , or depth of penetration , δ . the skin depth in meters is given by the following equation : where ω = 2π frequency ( in hz ), μ is the permeability ( or rate of absorption ) of the very conductive metal in henrys / meter , and σ is the conductance in mhos / meter . similarly , the base metal forming the center conductor 55 in the ablation needle 35 may be coated with a layer of a very conductive metal preferably to a thickness of at least the skin depth . to complete the coaxial transmission line 50 , the ablation needle 35 and the delivery needle 10 are coupled together using a first connector 70 on the delivery needle 10 and a second connector 65 on the ablation needle 35 . the first and second connectors 70 and 65 may be implemented in many different ways . for example , in a preferred embodiment , illustrated in fig1 a through 1 c , the first connector 70 on the delivery needle 10 comprises an outer contact 72 for a coaxial connector 75 at the proximal end of the delivery needle 10 . similarly , the second connector 65 on the ablation needle 35 comprises an inner contact 69 for coaxial connector 75 at the proximal end of the ablation needle 35 . the second connector 65 on the ablation needle 35 further comprises a connector dielectric material 36 surrounding a portion of inner contact 69 . additional connector dielectric material 39 may optionally line a portion of the lumen of outer contact 72 . first and second connectors 70 and 65 are adapted to connect together to form a coaxial connector 75 after the ablation needle 35 is inserted in the proximal port 15 of the delivery needle and distally displaced to bring the connectors 65 and 70 into contact . the adaptations on the connectors 65 and 70 may comprise a number of embodiments . for example , as shown , external threads 37 may be provided in the connector dielectric material 36 and internal threads 38 may be provided in the connector 70 to allow second connector 65 to threadably engage first connector 70 . in such an embodiment , a suitable assembly tool 56 for use in threadably engaging connectors 65 and 70 is illustrated in fig2 . the assembly tool 56 includes tabs 57 for engaging slots ( not illustrated ) in the dielectric material 36 of the second connector 65 . to complete assembly , a clinician would distally displace the ablation needle 35 within the lumen 20 of the delivery needle 10 until the threads 37 and 38 contact each other . the clinician would then insert the tabs 57 of the assembly tool 56 into the slots of the dielectric material 36 and rotate the assembly tool 56 to threadably engage threads 37 and 38 , completing the formation of the coaxial connector 75 . those of ordinary skill in the art will appreciate the numerous ways in which connectors 65 and 70 may engage one another to form coaxial connector 75 . for example , rather than using threads 37 and 38 , a latching mechanism using biased tabs engaging matching grooves may be employed . regardless of the manner in which connectors 65 and 70 connect together , the result is that the inner contact 69 of the coaxial connector 75 electrically couples to the center conductor 55 of the ablation needle 35 . similarly , the outer contact 72 electrically couples to the outer conductor 16 of delivery needle 10 . as used herein , “ electrically coupled ” shall indicate a coupling capable of conducting current at microwave frequencies . in this fashion , a microwave power source ( not illustrated ) coupled to the coaxial connector 75 will transmit energy through the coaxial transmission line 50 to the microwave antenna 40 . first connector 70 , and therefore coaxial connector 75 , further comprises a nut 68 having internal threads 73 or other mechanical means for insuring firm connection between the coaxial connector 75 and a flexible coaxial cable coupled to the microwave power source . nut 68 freely rotates about delivery needle 10 . in an alternative embodiment , first and second connectors 70 and 65 , illustrated in fig1 f and 1 g , the ablation needle 35 further comprises a proximal coaxial extension 80 . a center conductor 81 of the coaxial extension 80 is electrically coupled to the center conductor 55 in the ablation needle 35 . the coaxial extension 80 includes an outer conductor 82 that ends distally in the second connector 65 . the coaxial extension 80 ends proximally in coaxial connector 76 . the delivery needle 10 ends proximally in the first connector 70 such that when the first and second connectors 70 and 65 and connected , the outer conductor 82 of the coaxial extension 80 is electrically coupled to the outer conductor 16 of the delivery needle 10 . in this fashion , microwave energy coupled to the coaxial connector 76 electrically couples to the coaxial transmission line 50 through the coaxial extension 80 . the first connector 70 may comprise threads 71 on the outer surface of the outer conductor 16 . similarly , the second connector may comprise threads 67 on the inner surface of the outer conductor 82 wherein threads 71 and 67 are adapted to threadably engage one another . those of ordinary skill in the art will appreciate that alternate means such as the biased tabs and matching grooves previously described may be used instead of threads 71 and 67 . regardless of whether the ablation needle 35 and the delivery needle couple together to create the coaxial transmission line 50 , to minimize trauma and bleeding , particularly in organs like the liver that tend to bleed , the delivery needle 10 is preferably 17 gauge or higher . however , as illustrated in fig1 e , although the delivery needle 10 may have a distal portion 14 that is 17 gauge or higher , a proximal portion 13 of the delivery needle 10 may be thicker in diameter , for example , 12 gauge or less . only the distal portion 14 would penetrate sensitive tissue such as the liver ; the proximal portion 13 may either not penetrate the body at all ( as in an open surgical procedure ) or may penetrate only skin and muscle such as during a percutaneous procedure . the added diameter in the proximal portion 13 allows the proximal portion of the coaxial transmission line 50 to have a larger diameter and therefore be less lossy . the larger diameter also helps to improve rigidity in the proximal portion 13 . furthermore , in some embodiments such as those of fig1 - 15 , it allows greater maneuverability of the biopsy and ablation needles through delivery needle 10 . it is to be noted that as the outer diameter of delivery needle 10 changes from that in proximal portion 13 to the diameter of distal portion 14 , the diameter of lumen 20 also may change accordingly . in addition , the outer diameter of the dielectric material 60 of ablation needle 35 would change accordingly to create the coaxial transmission line 50 . turning now to fig2 the hollow delivery needle 10 may include an obturator 11 adapted to be slidably disposed within the lumen 20 . the obturator 11 includes a proximal handle 12 . with the obturator 11 inserted in the lumen 20 through the proximal port 15 , the handle 12 acts as a stop , engaging the proximal port 15 on the delivery needle 35 and preventing further distal displacement of the obturator 11 . thus , the obturator may provide additional support for the delivery needle and assist in piercing tissue , particularly for hard tumors . to reach liver tumors , the delivery needle 10 may extend distally 15 to 20 centimeters from the proximal port 15 . the delivery needle 10 may have a jacket 17 of an insulating material such as parylene or teflon ® on its outer surface . the biopsy needle 30 may be of either an aspirating or coring type as is well known in the art . note that the biopsy needle 30 may have a proximal handle 45 . when the biopsy needle is inserted into the proximal port 15 of the delivery needle 10 , the proximal handle 45 abuts against the proximal port 15 , preventing further distal displacement within the lumen 20 . the biopsy needle 30 may have a blunt distal end 31 or a sharpened distal end 32 . in addition , the biopsy needle 30 may further comprise a stylet 29 having a matched point 34 to aid in strengthening or stiffening the biopsy needle 30 and assist piercing tissue with the needle 30 . the biopsy needle 30 is preferably 20 to 23 gauge and most preferably 20 to 21 gauge . the lumen of the biopsy needle 30 is preferably greater than 0 . 017 ″ and most preferably at least 0 . 022 ″. the biopsy needle 30 may be inserted into the lumen 20 of delivery needle 10 and both inserted into tissue as a unit such that the biopsy needle 30 acts as an obturator 11 . use of either a biopsy needle 30 or the obturator 11 in this way allows the delivery needle 10 to have a flat distal end , lessening trauma to internal organs from movements of the delivery needle 10 during exchange of the biopsy needle 30 and the ablation needle 35 . turning now to fig3 a through 3 e , the microwave antenna 40 , formed by the distal projection of the ablation needle 35 , may take any of several well - known forms in the art . for example , fig3 a and 3 b illustrate embodiments in which the microwave antenna comprises a monopole antenna 41 as described by labonte et al ., “ monopole antennas for microwave catheter ablation ,” ieee trans . microwave theory tech ., vol . 44 , no . 10 , pp . 1832 - 1840 , october 1996 , the contents of which are hereby incorporated by reference . in such embodiments , the distal projection of the ablation needle comprises the previously described center conductor 55 surrounded by the dielectric material 60 . if , as illustrated in fig3 a , the center conductor 55 extends to the distal end of the distal projection , thereby contacting tissue when in use , the monopole antenna 41 is referred to as an open - tip monopole antenna . in other embodiments , a tip 42 prevents the center conductor 55 from directly contacting tissue as illustrated in fig3 b . if the tip 42 comprises a dielectric material , the monopole antenna 41 is referred to as a dielectric - tip monopole . if the tip 42 comprises a metallic material , the monopole antenna 41 is referred to as a metal - tip monopole . alternatively , the distal projection of the ablation needle 35 may form a dipole antenna 43 as illustrated in fig3 c and 3 d . in such embodiments , the distal projection of the ablation needle 35 comprises the center conductor 55 and surrounding dielectric material 60 as previously described . in addition , the distal projection of the ablation needle includes an outer conductor 44 forming one or more sections of coaxial transmission line in combination with the center conductor 55 . this outer conductor 44 is electrically isolated from the delivery needle 10 . it may be electrically coupled to the center conductor 55 as shown in fig3 c or may be electrically isolated from it as shown in fig3 d . in yet another embodiment , the distal projection of the ablation needle 35 may form a helical coiled antenna 51 . the helical coiled antenna 51 comprises the center conductor 55 and surrounding dielectric material 60 as previously described . in addition , the center conductor 55 has an extension that forms coils 52 about the dielectric material 60 . the coils 52 are electrically isolated from the delivery needle 10 . stauffer et al ., ( 1995 ) interstitial heating tech . in : seegenschmiedt et al . ( eds . ), thermoradiotherapy and thermochemotherapy , vol . 1 , springer , pp . 279 - 320 provide additional discussion of suitable dipole 43 and helical coil antennas 51 , the contents of which is hereby incorporated by reference . turning now to fig1 through 15 , an alternate embodiment of the present invention in which the ablation needle 35 and the delivery needle 10 do not couple together to create the coaxial transmission line is illustrated . the hollow delivery needle 10 possesses a proximal port 15 opening into a lumen 20 which extends through the delivery needle 10 to an open distal end as described previously . in addition , the delivery needle 10 preferably has a jacket of an insulating material such as parylene or teflon ® at least partially surrounding its outer surface ( illustrated in fig1 a ) or may be formed completely of a nonconductive material such as plastic . the delivery needle 10 is preferably 17 gauge , more preferably 18 gauge or higher . the ablation needle 35 is longer than the delivery needle 10 such that when the ablation needle 35 is inserted into the proximal port 15 and displaced until a stop 83 located on the ablation needle 35 engages the proximal port 15 , a distal projection of the ablation needle 35 will extend from the distal end of the delivery needle 10 . the distal projection of the ablation needle is adapted to form a microwave antenna 40 . the ablation needle 35 includes a transmission line to couple to the microwave antenna 40 . in the embodiment illustrated in fig1 , the transmission line in the ablation needle 35 comprises a coaxial transmission line 61 . however , other types of transmission lines as known in the art may be used in ablation needle 35 . to form the coaxial transmission line 61 , the ablation needle 35 includes the center conductor 55 and surrounding dielectric material 60 as previously described . in addition , the ablation needle 35 includes an outer conductor 62 that circumferentially surrounds the dielectric material 60 to complete the coaxial transmission line 61 . this outer conductor 62 extends distally from a coaxial connector 78 to the microwave antenna 40 and preferably comprises a highly conductive metal of a thickness of 1 to 10 times the skin depth ( δ ) as described herein . outer conductor 62 preferably is protected by an outer coating of a material such as a fluoropolymer or parylene . because ablation needle 35 includes the complete coaxial transmission line 61 and coaxial connector 78 , the delivery needle 10 requires no electrical connector , and need merely end in the proximal port 15 through which the ablation needle 35 is inserted . the ablation needle 35 is distally displaced within the lumen 20 of the delivery needle 10 until the stop 83 , here provided by the coaxial connector 78 , prevents further distal displacement by contacting the proximal end of the delivery needle 10 . in addition to acting as a stop 83 , the coaxial connector 78 may be modified to connect to the proximal end of the delivery needle 10 through appropriate connectors ( not illustrated ). when the ablation needle 35 is displaced to contact the stop 83 with the proximal end of the delivery needle 10 , the distal projection of the ablation needle 35 extends beyond the distal end of the delivery needle 10 . this distal projection forms a microwave antenna 40 . the microwave antenna 40 may be a monopole 41 , dipole 43 or helical coil 51 as previously described and illustrated in fig3 a through 3 c . if center conductor 55 and outer conductor 62 are not comprised of a highly conductive metal , the center conductor 55 and the inner surface of the outer conductor 62 may be coated with a highly conductive metal to a thickness as previously described . to minimize trauma during insertion and ablation , the delivery needle 10 is preferably 17 gauge or higher , more preferably 18 gauge or higher . as an alternative embodiment , instead of the coaxial connector 78 , the delivery needle 10 may include a connector ( not illustrated ) comprising an outer portion of a coaxial connector and the ablation needle 35 may include a connector ( not illustrated ) comprising an inner portion of a coaxial connector . when the connectors are connected , the resulting coaxial connector is electrically coupled to the coaxial transmission line 61 . in such an embodiment , the outer portion of the coaxial connector would have to electrically couple to the outer conductor 62 of the ablation needle 35 . it is to be noted that , regardless of the particular type of microwave antenna 40 implemented , the present invention provides advantages over prior art microwave antennas . in the present invention , the biopsy needle 30 and the delivery needle 10 may have already formed an insertion track before the microwave antenna 40 is inserted into an ablation site . because the microwave antenna 40 may follow the existing insertion track , the microwave antenna 40 may possess a flat distal end . prior art mct microwave antennas typically had a sharpened distal end so that these antennas could be inserted into an ablation site . the sar pattern of a microwave antenna 40 may be altered depending upon whether a flat or sharpened distal end is utilized . thus , the present invention allows a clinician more control of the sar patterns needed for a particular therapy . whether the ablation needle 35 and the delivery needle 10 are coupled to create the coaxial transmission line 50 or the ablation needle 35 includes the coaxial transmission line 61 , the present invention will provide a variety of microwave antennas 40 which are inserted into a tumor through the lumen 20 of the delivery needle 10 . the delivery needle 10 and the microwave antenna 40 together follow an insertion track in the body . the microwave antenna 40 may take a number of forms as previously described . each of the forms , such as the monopole 41 , has an effective antenna length which represents the longitudinal extent of tissue ablated by the microwave antenna 40 in the insertion track . the effective antenna length may depend upon the antenna design , the expected insertion depth , the expected amount of tissue perfusion , the expected duration and power of energy deliver , the frequency of the microwave power source , and additional factors . tumors , such as liver tumors , can “ seed ” an insertion track as the microwave antenna 40 is withdrawn from the tumor . therefore , it is beneficial to ablate the insertion track during withdrawal to kill any tumor cells displaced along the insertion track which would otherwise ( potentially ) act as “ seeds ” for future tumors . moreover , track ablation helps to stem hemorrhage from the insertion track . after performing ablation of a tumor , the microwave antenna 40 may be withdrawn approximately an effective antenna length . ablation would then be performed again , thus performing ablation in the insertion track without gaps and without excess overlap between successive ablations so as to kill displaced tumor cells while minimizing excess damage to the insertion track . because only a small area surrounding the insertion track need be ablated , and to minimize damage to healthy tissue during track ablation , the clinician may decrease the diameter of the field of the antenna and / or lengthen the field to speed track ablation time . these alterations to microwave field diameter and length may be made by decreasing the power or frequency of the microwave power source . in addition or alternatively , the antenna field may be altered by changing the physical dimensions of the microwave antenna 40 by , for example , proximally or distally displacing the ablation needle 35 within the lumen 20 of the delivery needle 10 . to assist coupling a microwave power source to the microwave antenna 40 , the coaxial connector 75 , 76 and 78 as used in the various embodiments described herein may comprise a standard coaxial connector such as an sma connector . alternatively , the coaxial connector may be a coaxial connector of a custom design for ease of assembly . the present invention also includes a system for biopsy and ablation of tumors . the system comprises a modular needle apparatus in one of the various embodiments as described herein . an example system is illustrated in fig2 . this system includes the delivery needle 10 and ablation needle 35 of fig1 a and 1 c . also included is an obturator 11 , a biopsy needle 30 and a stylet 29 with a matched point 34 for the biopsy needle 30 . a syringe 58 is shown for coupling to the biopsy needle 30 during aspiration of a tissue sample . as discussed herein , an assembly tool 56 aids the connection of the ablation needle 35 and the delivery needle 10 . the system would further comprise a microwave power source 59 for coupling to the modular needle apparatus by connecting to the coaxial connector 75 . the microwave power source will preferably generate microwave energy in the frequency range of 0 . 3 to 3 . 0 ghz . more preferably , the microwave antenna 40 and the microwave power source are adapted to operate at 0 . 915 or 2 . 45 ghz . the particular frequency or frequency range generated by the microwave power source will affect the sar pattern of the microwave antenna 40 . the clinician may thus adjust the microwave power source to generate a desired sar pattern as required by a particular tumor . the present invention includes methods of biopsy and ablation using the disclosed modular needle apparatus . turning now to fig4 - 12 , a method of biopsy and ablation is illustrated using the modular needle apparatus as shown in fig1 a - 1 c . as discussed herein , this embodiment creates the coaxial transmission line 50 after connecting together connector 65 on the ablation needle 35 to connector 70 on the delivery needle 10 . as illustrated in fig3 the delivery needle has an obturator 11 in the lumen 20 to stiffen the delivery needle 35 and assist piercing of tissue . preferably , a percutaneous procedure is performed . if , however , a laparoscopic procedure is performed , the delivery needle 10 may be introduced through a trocar ( not illustrated ). moreover , in an open surgical procedure , the delivery needle would enter tissue through an incision rather than entering percutaneously . the clinician may monitor the procedure with an imaging device such as mri or ultrasound to guide the insertion of the delivery needle 10 into a patient until the delivery needle 10 is suitably positioned with respect to a tumor 95 located within the liver 90 . such a suitable position will depend upon the shape and position of the tumor 95 and the sar pattern of the particular microwave antenna 40 used . having inserted the delivery needle 10 properly with respect to the tumor 95 , the clinician may withdraw the obturator 11 as illustrated in fig4 and 5 . the clinician is now ready to perform a biopsy of the tumor 95 using a biopsy needle 30 inserted through the lumen 20 of the delivery needle 10 . the clinician may perform this biopsy in a number of ways . for example , the biopsy needle 30 may be distally displaced within the lumen 20 until the distal end of the biopsy needle protrudes from the delivery needle 10 into the tumor 95 . alternatively , as illustrated in fig6 the clinician may distally displace the biopsy needle within the lumen 20 until the distal end of the biopsy needle is proximally adjacent the distal end of the delivery needle 10 . the clinician then exposes the distal end of the biopsy needle to the tumor 95 so that a tissue sample may be taken by proximally withdrawing the delivery needle 10 with respect to the biopsy needle 30 as illustrated in fig7 . as an alternative to the steps shown in fig4 - 7 as described thus far , biopsy needle 30 may be introduced with delivery needle 10 as a unit , and would appear as in fig7 . in that case , biopsy needle 30 preferably has a stiffening stylet 29 with a matched point 34 to aid in piercing tissue , particularly hardened tumors . to further aid in stiffening the biopsy needle 30 , the biopsy needle 30 would preferably have a diameter very close to the inner diameter of delivery needle 10 . the biopsy stylet 29 is then removed so that a biopsy can be taken . in either case , the biopsy needle 30 preferably comprises a luer - type fitting 33 on its proximal end . a syringe ( illustrated in fig2 ) is attached to fitting 33 and suction is applied to draw tissue into biopsy needle 30 . after drawing a tissue sample into biopsy needle 30 , the biopsy needle 30 is withdrawn from the lumen 20 of the delivery needle 10 as illustrated in fig8 . the clinician may optionally perform an additional biopsy , either at this point or following an ablation using the same or a different biopsy needle 30 . should the biopsy result indicate that the tumor 95 requires ablation , the clinician proceeds to insert the ablation needle 35 into the lumen 20 of the delivery needle 10 . ( alternatively the clinician need not wait for the result ). as described previously , the clinician distally displaces the ablation needle 35 within the lumen 20 until the second connector 65 on the ablation needle 35 is coupled to the first connector 70 on the delivery needle 10 . in this fashion , a coaxial connector 75 is formed as illustrated in fig9 so that microwave power source may be coupled through the coaxial transmission line 50 to the microwave antenna 40 . note that the insertion of the microwave antenna 40 into the tumor 95 does not require removal of the delivery needle 10 . thus , the clinician need not have to reinsert the delivery needle after a biopsy , avoiding the uncertainties of trying to align the delivery needle 10 with the previously formed insertion track . furthermore , because the microwave antenna 40 follows the insertion track left by the biopsy needle 30 , the microwave antenna 40 need not have a sharpened distal end . however , the present invention also contemplates methods wherein the clinician performs ablation before or in lieu of performing a biopsy or in a slightly different location than the biopsy site . in such an embodiment of the invention , the microwave antenna 40 would preferably have a sharpened distal end because the microwave antenna 40 will not be following a biopsy needle track . turning now to fig1 , the clinician couples a microwave power source to the coaxial connector 75 through , e . g ., a flexible coaxial cable 100 . at this point the clinician may begin ablating the tumor 95 . as illustrated in fig1 , the ablation continues until the area of ablated tissue 110 is larger than the tumor , thus insuring that the entire tumor 95 is destroyed . finally , as illustrated in fig1 , the clinician may perform track ablation as previously described . the clinician partially withdraws the delivery needle 10 before performing another ablation . repeated partial withdrawal and ablation steps are performed to completely ablate the insertion track . many widely differing embodiments of the present invention may be constructed without departing from the spirit and scope of the present invention . therefore , it should be understood that the present invention is not to be limited to the particular forms or methods disclosed , but to the contrary , the present invention is to cover all modifications , equivalents and alternatives falling within the spirit and scope of the appended claims .
a modular biopsy , ablation and track coagulation needle apparatus is disclosed that allows the biopsy needle to be inserted into the delivery needle and removed when not needed , and that allows an inner ablation needle to be introduced and coaxially engaged with the delivery needle to more effectively biopsy a tumor , ablate it and coagulate the track through ablation while reducing blood loss and track seeding . the ablation needle and biopsy needle are adapted to in situ assembly with the delivery needle . in a preferred embodiment , the ablation needle , when engaged with the delivery needle forms a coaxial connector adapted to electrically couple to an ablating source . methods for biopsying and ablating tumors using the device and coagulating the track upon device removal are also provided .