preferred embodiments of the invention include an electrode 99 which comprises at least one longitudinal electrical conductor 20 having a proximal end and a distal end as schematically illustrated in fig1 ( a - i ). the electrode 99 further comprises a tissue cutting tip ( itself comprising a linking electrical conductor such as the tissue cutting loop 32 ) coupled to at least one of the longitudinal electrical conductors 20 proximate the conductor &# 39 ; s distal end . an electrode further comprises at least one at least partially convex tissue skid 26 , which may be coupled to at least one electrical conductor 20 . tissue skids may be metallic ( that is , electrically conductive ), in which case each such tissue skid is electrically insulated to prevent inadvertent electrical contact with electrical conductors of the electrode . skids may also be electrically nonconductive so that preventive electrical insulation is unnecessary . electrical insulation 23 is optionally part of a longitudinal electrical conductor 20 where needed to prevent undesired electrical contact , and note that an outer metal tube 21 may be fitted over the insulation 23 for added stiffness and / or for firm coupling ( as by molding , welding or soldering ) to a resectoscope guide tube or analogous substantially rigid member to form a stabilizer assembly . alignment force is transmitted from tissue contacted by a skid to the skid , and through the skid to the electrode via at least one skid coupling means . skid coupling means include , for example , snap - fit , friction - fit , press - fit , clip - on , swaged - on , molded - on , molded - in , or adhesively - attached couplings , and the position of a skid coupling means on an electrode may be either adjustable or substantially non - adjustable in use . tissue skids may be coupled to any portion of an electrode where application of lateral forces is desired . in preferred embodiments , a skid may be coupled to both of two substantially parallel and insulated longitudinal electrical conductors adjacent to the distal ends of the conductors ( that is , adjacent to a tissue cutting tip as in fig1 d ) or proximal to this location as in fig1 b . preferred sizes for contact areas of tissue skids may be determined depending on several factors , including the type of tissue to be resected , the size of the cutting tip , and the magnitude of lateral forces desired . skids exert reaction forces on tissue which are proportional to the lateral forces exerted on the electrode to which they are coupled . effective positional control of the electrode therefore requires that pressures applied to tissues not cause significant displacement of the tissue adjacent to a skid . for example , electrodes suitable for resection of endometrial tissue may have two skids within about 30 mm of a cutting tip with a total minimum skid tissue contact area preferably within a range of about 4 to 100 mm 2 , depending in part on actual skid - tip distance . skids immediately adjacent to a cutting tip in this application preferably have individual surface areas of about 3 to about 10 mm 2 . whether electrically conductive or nonconductive , tissue skids 27 may be located near the distal ends of the longitudinal electrical conductors , substantially adjacent to the tissue cutting tip ( as in fig1 d ). in this case , a preferred form for the skids would be substantially spherical ( as schematically illustrated ), with the linking conductor of the cutting tip protruding through at least one skid . however , skids may also be ( or may instead be ) located at a support point proximal to the cutting tip , preferably about two - thirds to three - fourths of the distance from the proximal to the distal end of the electrode . if the electrode comprises two longitudinal conductors , they may be coupled by a stabilizer assembly , the stabilizer assembly preferably being located at the above support point and thus furnishing a convenient location for coupling one or more skids to the electrodes . note that a skid may also comprise the end portion 39 of cooling means 36 as shown in fig2 c . this end portion may be conductive or a layer of insulation contiguous with that of longitudinal conductor 20 , 20 &# 39 ;, 20 &# 34 ; may extend over end portion 39 to make the resulting skid electrically nonconducting . in the electrode embodiments schematically illustrated in fig1 ( a - i ), the stabilizer assembly comprises a guide tube 24 through which the distal end of an endoscope may be inserted . when the endoscope is a rigid tube resectoscope ( not shown ), a portion of the rigid tube proximal to that within the guide tube 24 may by further stabilized with respect to the electrode by its reversible insertion in the spring guide clip 22 . a resectoscope ( not shown ) adapted for use with electrodes of the present invention would typically comprise a channel to allow the introduction of a ( typically ) nonconducting irrigation fluid ( which also serves as a cooling fluid ) to the vicinity of a tissue cutting tip comprising cooling means ( see fig2 ( a - c )). note that fluid flowing from the end of a resectoscope inserted within guide tube 24 will tend to strike and flow around cooling means 36 . in particular , fluid flowing over the surface of cooling means 36 would be exposed to the increased surface area represented by grooves 37 , and heat transfer from cooling means 36 to the fluid ( not shown ) would be increased as a function of the increased surface area . analogous increases in heat transfer may be obtained if grooves 37 are replaced or supplemented with other augmented heat transfer surface means , as described above . heat transfer from cooling means 36 to a cooling fluid flowing around cooling means 36 may also be increased if cooling means 36 comprises relatively better heat conductors ( such as the metals copper and silver ). to even further enhance total heat transfer from cooling means 36 , a heat transfer fluid may be incorporated in a hollow portion of cooling means 36 as schematically illustrated in fig3 . such a heat transfer fluid would preferably be one which is relatively easily vaporized at the temperatures which electrosurgery would induce in the portions of cooling means 36 in contact with tissue being electrically ablated . the fluid would also preferably be nonflammable and relatively nontoxic in the quantities found in cooling means 36 , and be easily condensed at the temperature of cooling fluid which may be flowed over cooling means 36 . such a fluid might be chosen from the various liquid halogenated anesthetic agents approved for use in humans ( such as halothane , enflurane , desflurane or sevoflurane ). fig3 schematically illustrates the preferably continuous process of evaporation of cooling fluid ( a cooling process ), and cooling fluid vapor condensation , which is a heat transfer process to the grooves 37 and thus to whatever external cooling agent ( not shown ) is in contact with the grooves 37 . note that in fig3 cooling means 36 is electrically connected to longitudinal electrical conductors 20 , each comprising a central metallic conductor 10 ( such as copper or nickel silver ) with appropriate insulation 23 sufficient to prevent inadvertent electrical contact with the central metallic conductor 10 . note also that the illustrated grooves 37 are only examples of the variety of augmented heat transfer surface means which can be used to enhance heat removal from cooling means 36 . another way of removing heat from a tissue cutting tip with cooling means is by use of cooling means 38 , as schematically illustrated in fig4 . in contrast , to cooling means 36 , which is designed to facilitate heat transfer to an externally applied cooling fluid , cooling means 38 is designed to facilitate heat transfer to an internal cooling fluid which is subsequently removed from cooling means 38 . the internal cooling fluid ( for example , pressurized carbon dioxide ) is admitted to cooling means 38 through a hollow central electrical conductor 40 ( a part of longitudinal electrical conductor 20 &# 39 ;) which is electrically insulated as above with insulation 23 . the compressed cooling fluid ( not shown ) is allowed to expand through orifice 44 and thus to cool . the cooled expanded cooling fluid ( not shown ) then absorbs heat by contact with the interior surface of cooling means 38 and exits ( preferably ) through an outlet comprising a hollow central electrical conductor 40 &# 39 ; ( a part of longitudinal electrical conductor 20 &# 34 ;). note that where embolization of expanded cooling fluid would not pose a significant clinical risk , one or more outlets from the cooling means may be provided in the region of electrosurgery .
an electrode having at least one self - guiding surface for use in electrical tissue resection . self - guiding forces are applied substantially perpendicular to the longitudinal axis of the electrode , and / or rotationally about the longitudinal axis . forces sufficient to compensate in part for errors in cutting tip placement are produced by tissue pressure acting on one or more convex tissue skids . optional tissue cutting tips for the electrode are configured to enhance heat transfer from the cutting tip by external fluid flow around the cutting tip , to improve heat transfer within the cutting tip through use of heat transfer fluids and / or heat - conducting solids , and / or to cool the cutting tip by expansion of a compressed cooling fluid through an orifice within a hollow portion of the cutting tip .