in the following description , the same reference numbers are used for the same and similarly acting parts . fig1 shows the essential components of an electrosurgical device according to the disclosed embodiments . an ablation probe 10 is typically supplied with fluid from a fluid source 40 . in order to adjust a prescribed inlet pressure p 1 and / or outlet pressure p 2 , the fluid source 40 is in fluid connection with a fluid regulating device 42 , which can include a plurality of valves and measuring sensors . a high - frequency generator 30 is in electrical connection with the ablation probe 10 and provides a high - frequency current which is applied via appropriate electrodes 16 , 16 ′ ( see fig2 ) or 16 ″ ( see fig4 ) to a tissue 1 to be treated . the electrosurgical device also includes a controller 50 which controls the high - frequency generator 30 and the fluid regulating device 42 . the controller 50 receives signals from an operating unit 60 , via which the treating physician can make settings on the electrosurgical device . for example , the coagulation process can be started via the operating unit 60 . fig2 shows a first example embodiment of an ablation probe 10 . the probe is a bipolar ablation probe 10 which has a first electrode 16 and a second electrode 16 ′. both electrodes 16 , 16 ′ are located in a distal region of a probe body 12 , close to a probe tip 11 . the two electrodes 16 , 16 ′ are electrically insulated from one another . as soon as a high - frequency current is applied to the electrodes 16 , 16 ′, a current distribution field is formed in the tissue 1 contacting the ablation probe 10 . provided the tissue 1 is homogeneous , this current distribution field is configured essentially spherically , wherein the current density decreases with increasing distance from the probe body 12 . in the tissue , the high - frequency current performs work , which is manifested in the form of heat energy . depending on the structure of the tissue 1 , a heat distribution field is formed . within the heat distribution field is a region in which the temperature increase is sufficiently high that the tissue becomes devitalized . this region is defined as the coagulation zone 4 . irregular structures in the tissue 1 , such as blood vessels , lymph ducts or organs can influence the current distribution field such that an asymmetrical heat distribution field is produced . an asymmetrical heat distribution field , and consequently an asymmetrical coagulation zone 4 , is often undesirable . in the example embodiment shown in fig2 , a blood vessel 2 is situated in the immediate vicinity of the ablation probe 10 . with conventional ablation probes 10 , this would result in a coagulation zone 4 having a high degree of asymmetry in the region of the blood vessel 2 . however , the ablation probe 10 according to the disclosed embodiments can counteract this effect . for this purpose , a second electrode 16 ′, situated proximally behind the first electrode 16 is more strongly cooled . the approximately symmetrical coagulation zone 4 shown in fig2 is thus formed . fig3 shows a further example embodiment of the ablation probe 10 . a blood vessel 2 is situated close to the first electrode 16 and thus in the immediate vicinity of the probe tip 11 . asymmetry of the coagulation zone 4 resulting therefrom can be counteracted by stronger cooling of the distal region of the ablation probe 10 , that is , of the first electrode 16 . therefore , considering the heat distribution on the probe body 12 , a maximum cooling performance ( minimum temperature ), which decreases in the proximal direction , is produced in the region of the probe tip 11 . distal introduction of the fluid into the evaporation region therefore results in a decreasing main pressure gradient in the proximal direction in the evaporation region . fig4 shows a further example embodiment of the ablation probe 10 . this is a monopolar probe 10 . the ablation probe 10 includes therefore only one electrode 16 . the second electrode for application of the high - frequency current is a neutral electrode 16 ″, which is applied over a large area on a surface of the tissue 1 . depending on the position and orientation of the ablation probe 10 relative to the large area neutral electrode 16 ″, a current distribution field is produced which depends on the distance between the electrodes 16 , 16 ″. in the example embodiment of fig4 , the current density in the tissue 1 close to the probe tip 11 is substantially higher than in regions which lie between a proximal end of the electrode 16 and the neutral electrode 16 ″. undesirable carbonization of the tissue 1 can therefore occur close to the probe tip 11 . in order to prevent this effect , the ablation probe 10 according to the disclosed embodiment cools the probe body 12 more strongly in the region close to the probe tip 11 . in particular , the distal region of the electrode 16 is more strongly cooled than a proximal region . positioning and orientation of the monopolar ablation probe 10 in which the proximal region of the electrode 16 must be more strongly cooled in order to create the most evenly decreasing heat distribution field possible are conceivable . it is important for the disclosed embodiments to be able to adjust the heat distribution at the probe body 12 of the ablation probe 10 . in particular , the ablation probe 10 can allow a maximum cooling effect to wander along the longitudinal axis thereof . it is therefore possible to set a maximum cooling zone at the tip 11 of the ablation probe 10 . alternatively , the cooling zone can be positioned close to the proximal end 17 of the electrode 16 . the example embodiments of an ablation probe 10 shown in fig5 to 7 enable adjustment or positioning of the cooling center by means of the inlet pressure p 1 . these ablation probes 10 include an evaporation region 20 in which a refrigerant evaporates and the ablation probe 10 , particularly the probe body 12 , extracts heat energy . the evaporation region 20 extends from the probe tip 11 in the proximal direction along the longitudinal axis of the ablation probe 10 . the coolant is introduced into the evaporation region 20 via an inlet 13 close to the probe tip 11 . since the boiling point depends , according to the refrigerant , on the prevailing pressure and the temperature , the refrigerant evaporates at the given temperature only when a pressure p 3 which is below the boiling pressure prevails in the evaporation region 20 close to the probe tip 11 . the evaporation region 20 includes a plurality of swirl elements 21 , 21 ′ which , according to fig4 , are arranged alternating in such a manner that , on the return route to the outlet 14 , the coolant has to pass individual lamellae which form the swirl elements 21 , 21 ′. as a result , turbulence is created . this turbulence improves , inter alia , the heat transfer between the refrigerant and the ablation probe 10 , while it also causes flow resistance which increases depending on the inlet pressure p 1 . thus , with a low inlet pressure p 1 just below the boiling pressure , there is only a low flow resistance . the refrigerant evaporates in the distal region of the evaporation region 20 close to an expansion nozzle 22 . the main pressure gradient therefore falls below the boiling pressure in the distal region of the evaporation region . with increasing inlet pressure p 1 , the flow resistance increases . this results in back - pressure , which increases in the distal direction of the evaporation region 20 . the swirl elements 21 , 21 ′ are arranged and configured such that the pressure p 3 decreases in the direction of flow . adjustment of the inlet pressure p 1 such that evaporation of the refrigerant only takes place after the last swirl element 21 ′ is thus conceivable . the pressure p 3 of the main pressure gradient therefore remains above the boiling pressure until said last swirl element 21 . through variation of the inlet pressure p 1 , the main pressure gradient of the pressure p 3 in the evaporation region 20 can be adjusted such that the zone of evaporation , that is , of maximum cooling can be positioned as desired . fig6 and 7 show further example embodiments of the swirl elements 21 , 21 ′. in fig6 , the evaporation elements 21 , 21 ′ are configured as a helix which winds round the inlet 13 . in fig7 , the swirl elements 21 , 21 ′ are configured with a saw - tooth form , projecting into the evaporation region . it should be noted at this point that all the aforementioned parts are claimed as essential to the invention both alone and in any combination , particularly the details shown in the drawings . amendments thereof are the common practice of persons skilled in the art .
an electrosurgical device for devitalizing tissue including a probe body , equipped with at least one electrode , and a cooling device . the probe body is suitable for generating a heat distribution field by means of a high - frequency current for devitalizing the tissue . the cooling device prevents carbonization of the tissue close to the probe body that would normally occur since the maximum current density occurs here . the electrosurgical device is modified such that the heat distribution over the probe body can be adjusted , allowing adjustment or positioning of a maximum cooling zone within the probe body . this regulation may be accomplished by regulating the inlet pressure of the refrigerant supply to the electrosurgical device .