the advantage of using double capacitors will be set forth herein in relation to an advantageous embodiment of the invention . here the advantages of the teaching according to the invention can be particularly clearly verified . if the efficiency is identified as the ratio of the delivered to the stored energy , it will be seen that the residual energy in the case of the parallel - serial connection only ever constitutes a quarter of that which is still stored on the individual capacitor . in the example with a tilt of 50 % the efficiency is 75 % in the case of the individual capacitor , whereas it is 93 . 75 % in the case of the two partial capacitors . the lower initial energy ( 80 %) is afforded by the lower residual energy ( 6 . 25 %) of the two partial capacitors . the individual capacitor needs 1 . 25 times the energy in order to achieve the same effect . heretofore the approach by way of the degree of utilization ( tilt ) in the calculation in equation ( 11 ) gave a relative ratio between c 1 and c 2 . if we ask which specific time constant rc 1 is concealed behind a 50 % tilt , attention is directed to table 1 at the end of this detailed description . specified therein for a tilt of 50 % is an rc 1 of between 6 . 4 and 6 . 6 ms , on average 6 . 5 ms , which with a defibrillation impedance of 50ω gives a preferred capacitance for the capacitor c 1 of 130 μf . the individual capacitor of the dual combination in accordance with equation ( 12 ) then has a capacitance of : in accordance with the invention therefore when settling for a time constant on the basis of a look - up table ( table 1 ) it is possible to determine the corresponding value for the pulse duration , tilt and efficiency for the individual capacitor . the partial capacitor corresponding thereto can then be ascertained with equation ( 11 ), for the parallel - serial use . this and the parameters resulting therefrom are summarized in table 1 from which it is possible to select the respective combination insofar as either the partial capacitor with an assumed load is predetermined , or a degree of efficiency which permits a large capacitor with at the same time a low voltage . in the foregoing example of the energy calculation for a 50 % tilt , it is possible to see that the levels of energy delivered are the same for both circuitry versions . that is due to the fact that the initial voltage and the mean voltage are equal for both versions . for a tilt of less than 50 %, the series connection of the partial capacitors during the residual discharge means that a higher voltage is produced than during the first phase so that the overall mean value of the voltage is higher with two capacitors . as it is not the delivered energy but the time integral in relation to voltage that is the crucial parameter in terms of defibrillation , the initial voltage can be reduced when using the double capacitors to the amount by which the voltage mean values increase . for tilts of greater than 50 %, the initial voltage in the case of the two - capacitor system will have to be set at a correspondingly higher level . the reduction in the capacitance of the two - capacitor system together with the increase in the mean voltage mean that the normalized stored energy ( nse 2 ) of a two - capacitor system above an rc - value which governs the 50 % tilt extends markedly more shallowly than the curve for the one - capacitor system ( see fig1 ). the curve for the normalized stored energy ( nse 1 ) of the one - capacitor system corresponds to the curve which is shown as fig8 in reference 4 from the background of the art , but which was there given with a normalized time constant . the normalized stored energy of the two - capacitor system ( nse 2 ) is afforded by multiplication from the reduced capacitance ( 2c 2 / c 1 ), the mean voltage altered by voltage doubling ( mv1 / mv2 ) and the nse 1 value of the one - capacitor system curve . the former simply arises out of equation ( 11b ) by forming the ratio of 2c 2 to c 1 , and multiplying it by the square of the ratio of the mean values of the voltages ( mv1 : mv2 ) 2 and the corresponding value of nse 1 ( see table 1 ). an example will illustrate this operating procedure . with a time constant rc 1 of 20 ms the tilt = 0 . 340 ( see table 1 ), and the normalized mean value of the voltage nmv 1 = 0 . 818 , which also applies in regard to parallel discharge of the two c 2 - capacitors . the mean value of serial discharge is 0 . 72 ( this follows from discharge to half the value ) multiplied by double the exponential final value of ( 1 - tilt ) corresponding to 0 . 66 , that is to say 0 . 72 · 1 . 32 = 0 . 95 . that gives an overall weighted mean value nmv 2 of ( 5 . 87 ms · 0 . 818 + 2 . 45 ms · 0 . 95 ): 8 . 32 ms = 0 . 857 ( duration of the parallel discharge = 5 . 87 ms , and that of the serial discharge = 2 . 45 ms , the overall duration = 8 . 32 ms ) which is 1 . 048 times higher than the mean value in the case of one - capacitor discharge . the initial voltage can be correspondingly lowered , which corresponds to a reduction in the stored energy to 0 . 911 . with equation ( 11b ) and by analogy with ( 12 / 13 ), it is possible to calculate for rc 1 = 20 ms an energy ratio e2 : e1 of 0 . 706 , which results in an overall reduction of 0 . 911 0 . 706 = 0 . 643 , or , to put that another way : the normalized stored energy of the one - capacitor system nse 1 of 2 . 591 is reduced in the case of the two - capacitor system to an nse 2 of 0 . 911 · 0 . 705 · 2 . 591 = 1 . 666 . for comparison : with a tilt of 50 % nse 1 = 1 . 46 and nse 2 = 1 . 17 ( see table 1 ). on the assumption that with a 50 % tilt with an rc 2 of 2 . 6 ms 10 j is required for defibrillation , the one - capacitor system with rc 1 of 6 . 5 ms would correspondingly require 12 . 5 j for the same effect . a two - capacitor system with a tilt of 34 % and an rc 2 of 7 . 06 ms would rise to 14 . 2 j and finally the one - capacitor system with rc 1 of 20 ms would rise to 22 . 1 j . the calculation once more demonstrates the finding that the pure energy information says nothing about the effectiveness thereof . in comparison with the example with a time constant of 20 ms , with an rc 1 of 10 ms the energy is reduced to only 0 . 966 (= 0 . 984 2 ) by virtue of the excessive increase in voltage , while as stated , with a 50 % tilt , there is no longer any difference as the mean voltage value is equal for both discharges . it follows therefrom that the new method fits in well in particular with the implementation of defibrillators with large capacitors and a correspondingly low voltage . investigations of three works ( references 5 - 7 ) in which the tilt was experimentally researched with a very low level of energy input showed that the energy with optimized tilt can actually be reduced to about 70 % in comparison with a tilt of 80 % ( in one experiment of 88 %). if consideration is further given to the reduction due to the two - capacitor system of for example 80 % for a 50 % tilt , then the highest mark of 30 j which was earlier established is reduced by the described two - capacitor systems to 0 . 8 · 0 . 7 · 30 j = 17 j with the same effectiveness . the maximum energy required would therefore fall still further if the capacitors were selected to be still smaller than the above - calculated 52 μf with a tilt of 50 %, which however involves increased voltages . thus for example a capacitor of 104 μf ( 2 · 52 μf ) requires just on 570 v in order to be charged up to the 17 j corresponding to the 30 j at an 80 % tilt value . therefore table 1 with the parameters nse 1 and nse 2 represents the required input in order to be able to effect defibrillation with the predetermined parameter ( this is generally the capacitor ) in comparison with the theoretically lowest delivered energy nde with an rc 1 of 2 . 36 ms ( in an 8 - digit calculation that value is to be unambiguously defined ). the input for nse 1 or nse 2 which can be read off as a function of the time constant rc 1 could also be interpreted as a reciprocal value which then can be interpreted as efficiency η in relation to the theoretical optimum . a horizontal line in graph 1 , that is to say a predetermined level of efficiency , demonstrates the possibility in relation to larger capacitors for the two - capacitor system or conversely it also shows that under some circumstances a one - capacitor system with an rc 1 of 9 ms can be more worthwhile than a two - capacitor system beyond an rc 1 of 20 ms . a vertical line clearly shows the lower degree of input ( or higher efficiency ) if the two - capacitor system were embodied instead of the one - capacitor system . the time constant rc 2 associated with the vertical line rc 1 can be read off in table 1 . the depicted two - capacitor system always reduces its residual voltage u2 ( residue ) to half the value of the corresponding one - capacitor system u1 ( residue ). that means however that the new system can only supply half the voltage for a bi - phase pulse . in accordance with the current school of thought this is deemed to be detrimental as the second phase is attributed with a crucial action which in our view it does not enjoy . nonetheless discharge of the residual voltage of the two - capacitor system is advantageous , preferably if that again happens in parallel . that would counteract in particular “ over - stimulation in the proximity of the cardiac electrode ” ( reference 4 ). how the delivered energy nde 1 of the one - capacitor system increases as a reference value with an increasing time constant ( lower curve ), how the stored energy nse 1 of the one - capacitor system increases over - proportionally with the time constant ( upper curve ), how the stored energy of the two - capacitor system nse 2 ( curve in the middle ) remains markedly below that of the one - capacitor system nse 1 , particularly when large time constants are involved , and how far away we are from the theoretical minimum nde 1 at rc 1 = 2 . 36 ms . while nse 1 or nse 2 represent the input which must be provided in relation to the theoretical minimum with a one - capacitor system or a two - capacitor system , the reciprocal η 1 = 1 / nse 1 and η 2 = 1 / nse 2 corresponds to the efficiency in which both electrical and also physiological optimization is expressed and which relates to the theoretical minimum of the delivered energy nde 1 with an rc 1 of 2 . 36 ms . fig2 is a representation of the discharge calculated with equation ( 12 ) at 50 % tilt for rc 1 and rc 2 . the rc 1 curve ends at t / rc = 0 . 9 ( in reality at 4 . 5 ms ) at a normalized voltage of 0 . 5 , while the exponential curvature can scarcely be perceived . that is also expressed in the mean normalized voltage nmv 1 which at 0 . 721 is only slightly lower than the linear mean value at 0 . 75 . “ mean value ” means that the wedge part of the discharge curve above the mean value line is equal in terms of surface area to that beneath the discharge curve . more specifically , in the total of three discharge curves with rc 1 , 2 · rc 2 and ½ · rc 2 it will be apparent , which has been theoretically worked out with formula ( 7 ), that the mean value of the voltage depends only on the tilt and not on the time constant . in all three discharges the wedge compensation effect is very beautifully demonstrated by the one line at 0 . 721 . that affords the same normalized voltage for both discharge curves and thus the same physiological effectiveness . fig3 predetermines an rc 1 discharge at 70 % ( tilt then 30 %, rc 1 = 27 . 5 ms ). the curve ends at an t / rc of 0 . 94 ( in actual fact at 9 . 8 ms ). at 0 . 625 ( 6 . 6 ms in reality ) the discharge is terminated with 2 · rc 2 and voltage doubling to the normalized value of 1 . 4 begins . after 2 . 8 ms the discharge procedure with ½ · rc 1 has then occurred again at 0 . 7 , and the line nmv 3 indicates the mean value which is 0 . 165 higher than that of the rc 1 curve . as a result the discharge with rc 2 and subsequent voltage doubling is physiologically more effective with the same initial voltage ( here 1 ). the effectiveness becomes the same if the initial voltage of the rc 2 curve is reduced to 94 % in relation to the rc 1 curve . in energy terms that denotes a reduction to 88 %. in this example however the efficiency η 2 at 0 . 53 ( see table 1 ) is already very low , which again is already reached by an rc 1 discharge at approximately an rc 1 of 11 . 5 ms ( corresponding to a tilt of 41 %). it is not only possible to deduce that for each time constant rc 1 there is an individual optimum tilt , but also how great the chronaxie time is , which in the calculation forms the important value for normalization of the system of equations . with knowledge of the optimum tilt and the corresponding time constant it is possible to ascertain from table a of [ 4 ], at which tilt which normalized time constant v = rc / chronaxie occurs . the chronaxie in relation to defibrillation of implanted units is to be fixed approximately at : estimates show that this value may individually alter by ± 30 %, which however has a less than 20 % effect on the results or upon optimization . if there should be a chronaxie which is markedly different from 2 ms , for example due to other electrodes or other defibrillation modes , it is nonetheless possible to use the results in table 1 , it is only necessary to multiply all time values by the factor c : the time constant rc 1 in the first column arises out of multiplication of the value v in table a from reference 4 with the chronaxie in accordance with equation ( 16 ) of 2 ms . the pulse duration t 1 in the second column is obtained like rc 1 from the value x in table a and chronaxie . the tilt was created in such a way that the first two columns in table a of ref . 4 were over - written with the new values for rc 1 and t 1 . nmv 1 is the mean value of the voltage as a function of rc 1 and during the pulse duration t 1 . a calculation formula was already afforded with equation ( 3 ). in deriving that formula the expression t 1 / rc 1 which occurs upon integration was replaced by the expression in [ u ( o ): u ( residue )]. the normalized mean voltage nmv 1 in accordance with equation ( 7 ) is thereby dependent only on the tilt . the normalized delivered energy nde 1 ( related to the minimum at rc 1 = 2 . 36 ms ) was obtained like tilt from table a of reference 4 . the efficiency eta from that table a was electrically defined as the ratio of delivered energy ( nde ) to stored energy ( nse ). the mode of operation of the method according to the invention is to be set forth in summarizing form once again hereinafter as follows : the normalized stored energy nse 1 is defined by the quotient nde 1 divided by eta . rc 2 is determined in accordance with equation ( 11a ). t ( 2 ) ( time during the discharge of rc 2 ) is calculated from the combination of equations ( 5 ) and ( 8 ): t ( 3 ) ( time during the discharge of the series circuit to half the voltage value ) is determined in analogous fashion : nmv ( 2 ) is the mean voltage during the time t ( 2 ) corresponding to equation ( 7 ). nmv ( 3 ) is the mean voltage during t ( 3 ) which with the equations ( 5 ) and ( 7 ) having regard to discharge to half the value is calculated as follows : nmv 2 is the voltage averaged over the times t ( 2 ) and t ( 3 ): mv1 : mv2 is the quotient which characterizes the increase ( or reduction ) in voltage on the basis of the parallel - series circuit configuration . 2c 2 : c 1 indicates the reduction in the stored energy in the case of the two - capacitor system in comparison with the one - capacitor system . nse 2 is the normalized stored energy which arises out of : the reciprocal value of nse 2 represents the efficiency η 2 which is related to the energy minimum nde 1 at rc 1 = 2 . 36 ms . nse 2 : nse 1 is identical to the ratio of the efficiencies η 1 : η 2 and demonstrates the superiority of the two - capacitor system in particular in relation to a high rc 1 . ( in the same manner , as indicated previously , it is also possible to calculate systems with more than two capacitors ). accordingly the combination of theoretically well - founded pulse duration or tilt with the principle of voltage doubling by means of two capacitors affords a technical advance which can be used in various ways . measurement of the time constant during parallel or sequential discharge can thus be advantageously used to ascertain the corresponding tilt and to cause the pulse to cease when it is reached . that applies both in regard to the individual capacitors and also in regard to the serial connection thereof . it is thus best possible to do justice to any situation with an unknown defibrillation impedance . all calculations were based on the assumption that the chronaxie in the defibrillation procedure is 2 ms . if that value should be found to be incorrect , for example fluctuating by up to 30 %, the method of the invention would not be rendered ineffective as a result as as a consequence the tilt changes by less than 16 %. that affords the advantageous development of making the tilt which is so important in terms of the effectiveness of the method variable by up to 20 % by programming . the curve nse 2 in fig1 demonstrates the input which is to be achieved with the two - capacitor system and which cannot be surpassed by any system known at the present day . the reciprocal of that value ( nse 2 − 1 ) defines the efficiency η 2 which gives the defibrillator its name . this therefore means not one defibrillator but a family which is dimensioned in accordance with the equations ( 11 ) for the two - capacitor system and which is optimized in the inverse relationship to the equation ( 22 ): η 2 = nse 2 − 1 = nse 1 − ·{ c 1 / 2c 2 }·{ nmv 2 / nmv 1 } 2 ( 25 ) c 1 / 2c 2 = ratio of the capacitances of the one — and two - capacitor systems respectively , all values are set out in table 1 as a function of the time constant rc 1 for the range between 1 . 0 ms and 100 ms . for the corner points of a realistic range of between 2 . 5 ms and 20 ms the eta values read as follows : η 2 ( 2 . 5 ms )= 0 . 969 ( 3 % more energy necessary in comparison with the reference value nde 1 ( 2 . 36 ms )), and η 2 ( 20 ms )= 0 . 60 , thus η 2 is higher by the factor of 1 . 56 than the reduction in input as shown in fig1 by virtue of two capacitors or the increase in efficiency ( as a reciprocal value of input ) η 2 is to be attributed exclusively to optimization of the pulse which in the case of a “ bi - phase ” pulse would correspond to the first phase . there is nothing against also discharging the residual voltage of the two - capacitor system as a second inverted phase , in which case that should preferably take place in the form of a parallel discharge . referring to fig4 an advantageous structural embodiment of the invention in the form of an implantable cardioverter defibrillator ( icd ) is shown in the form of a block circuit diagram . for operation thereof this embodiment thus also makes use of the method according to the invention . the block circuit diagram shows the co - operation in principle of the groups shown in the following figures . a defibrillator portion 1 produces the pulses which are to be delivered to the heart in a defibrillation phase and includes the energy source required for that purpose . the defibrillator portion 1 is connected to a control portion 2 containing the groups which establish the stimulation defibrillation times and determine the configuration in respect of time of the defibrillation pulses . a cardiac pacemaker portion 3 contains the usual functions of an implantable pacemaker and implements control in respect of time of the stimulation pulses which are necessary to maintain the normal cardiac activity in the bradycardia and tachycardia range . that also includes recognition of irregularities in cardiac activity from the intracardial electrocardiogram recorded by way of the implanted electrodes . the control portion 2 also has control over the pacemaker portion 3 so that in that way the functions thereof can also be remotely programmed and controlled in time - synchronized relationship with the behavior of the heart . the groups 1 through 3 are combined in a casing 4 which is represented symbolically by a broken line . the implanted portions which are disposed in the casing 4 are remotely controllable and remotely settable by a programming portion 5 from outside the body . in addition the configuration in respect of time of the cardiac events and the stimulation and defibrillation measures which are thereupon initiated is recorded in the control portion and if necessary can be transmitted by means of the programming portion to the exterior of the body and can there be evaluated by the doctor . fig5 shows in detail the functional components of the defibrillator portion 1 . in this case an energy source 11 which is in the form of a conventional battery serves as a power supply for this group . connected on the output side of the energy source 11 is a voltage transformer 12 which boosts the output voltage of the battery to a settable supply voltage u for charging up the subsequent capacitors c 1 and c 2 . the internal resistance of the voltage transformer 12 is such that charging - up of the capacitors c 1 and c 2 takes place in a suitably short period of time , after which in the situation requiring defibrillation it was activated by way of a suitable control line from the control portion 2 . the capacitors c 1 and c 2 can be connected by way of various switching elements s 11 through s 34 in various ways to the voltage transformer 12 on the one hand and the cardiac electrode 13 on the other hand , as is described in greater detail hereinafter . in this respect , activation of one or more of the switching elements s 11 through s 34 means that the switching element in question in switched into the conducting condition for a predetermined period of time . for the charging operation , the capacitors c 1 and c 2 are connected directly to the output of the voltage transformer 12 by activation of the switching elements s 11 and s 22 , so that the capacitors are charged up to their set initial voltage . in that case the charging operation is effected in a suitably short period of time according to the internal resistance of the voltage transformer . discharge of the energy stored in the capacitors c 1 and c 2 to the electrode 13 which is connected to the heart is effected either sequentially in respect of time by successive activation of the switching elements s 12 for c 1 and s 12 and s 24 for c 2 for two successive periods of time or by simultaneous activation of the corresponding switching elements in a single period of time . in this case , connection to the heart by way of the electrodes 13 is effected by activation of the switching elements s 31 and s 32 each in a first polarity . a further discharge configuration is afforded by a series connection of the capacitors c 1 and c 2 by activation of the switching elements s 22 and s 23 . in this case once again the switching elements s 31 and s 33 are activated for discharge in the first polarity . to reverse the discharge configurations for a possible residual discharge in the bi - phase mode of operation , the switching elements s 32 and s 34 are activated instead of the switching elements s 31 and s 33 . reference is now made to fig6 to describe the production of the controls signals , with the control portion 2 , which cause activation of the switching elements s 11 through s 34 for predetermined periods of time . the timer blocks shown in fig6 are respectively activated by a starting pulse by an input signal which is fed to the illustrated block from the left - hand side in the drawing . they respectively remain active for a predetermined period of time which is characteristic for the block and which can possibly be altered by way of external programming means ( programming portion 1 in fig1 ) and in that respect deliver a suitable control signal to the above - mentioned switching elements s 11 through s 34 of the defibrillator portion shown in fig5 . the signal connections in question leave the respective timer block upwardly in the drawing . after the expiry of the period of time which is characteristic of the respective timer block the timer blocks in question each output a control pulse which possibly serves for activation of a subsequent timer block . the corresponding signal paths leave the respective timer block towards the right in the drawing . when defibrillation is necessary , the timer block t 1 which determines the charging times of the capacitors c 1 and c 23 by means of control signals and the switching elements s 11 and s 22 is supplied with a suitable starting signal from a time control unit 21 which holds the supremacy in terms of time control . after charging is concluded that procedure is terminated by a suitable end signal to the timer block t 1 . the time duration of the charging procedure can possibly be set from the exterior , like also the charging voltage of the voltage transformer 12 in fig5 . the output signal of the timer block t 1 is fed to three and - gates 22 through 24 , to the further input of each of which passes a respective one of three control signals of the time control unit 21 , which select which of three subsequently connected timer blocks t 21 , t 22 or t 231 is activated by the output signal of the timer block t 1 . in this respect , the choice of the respective timer block determines which of three first discharge configurations is selected for the capacitors c 1 and c 2 . these are parallel discharge ( t 21 ), individual discharge ( t 22 ) and sequential discharge ( t 231 and t 232 ). in that way it is possible by means of the time control unit by virtue of external programming to establish which of the three first discharge configurations is adopted . in the case of the parallel discharge configuration being selected , the switching elements s 12 , s 22 , s 24 , s 31 and s 33 are activated by the time control unit t 21 . in contrast , in the case of the individual capacitor discharge configuration being selected , the switching elements s 12 , s 31 and s 33 are activated by the time control unit t 22 and , in the case of selection of the sequential discharge configuration , the switching elements s 12 , s 31 and s 33 are activated firstly — as in the above - mentioned case — by the time control unit t 231 . the control signals for termination of the signal output for the various timer blocks are produced by a control unit for discharge termination as indicated at 25 . that control unit determines the end of discharge of the capacitors c 1 and c 2 to provide for optimization in accordance with the invention of the discharge energy from the time constant arising in regard to discharge and the remaining residual discharge voltage which is ascertained in dependence thereon . ascertaining the discharge voltage in that way can be effected either by using a look - up table in the manner of table 1 in such a way that , after the time constant rc 1 has been ascertained the corresponding tilt value ( or that of the corresponding residual voltage ) is outputted , or that value is calculated on the basis of the specified relationships . to ascertain the appropriate operating parameters which are also used as an input parameter for the group 26 , the arrangement has a volt meter 26 which ascertains the current voltage at the electrodes 13 . the configuration of the voltage at the beginning of the discharge is taken — derived from the corresponding starting signal as the output signal of the time control block t 1 — with the beginning of the first phase of discharge of the capacitors c 1 and c 2 respectively , by means of a suitable group , to determine the time constant of the discharge procedure , which forms the product of the respective discharge capacitance and the resistance of the electrode 13 . the discharge voltage at which discharge is terminated depends on that time constant . that is effected with what is known as a look - up table in which the residual voltages at which the discharge is to be terminated in the respective phase are recorded in dependence on the ascertained time constant . that table is shown in greater detail as table 1 . when the voltage which is ascertained for the respective discharge configuration on the basis of the ascertained time constant is reached , a signal is delivered to the time control block which controls the discharge , that signal terminating the corresponding discharge time and possibly starting the next discharge phase by the appropriate control signal which indicates termination of the period of time in question . that is effected by activation of the subsequent time control block . in the case of sequential discharge , after discharge of the first capacitor c 1 to the ascertained discharge voltage , the second capacitor is discharged ( to the same discharge voltage ). for that purpose , the block t 232 is activated by the output signal of the block t 231 and activates the switching elements s 22 , s 24 , s 31 and s 33 . termination of that discharge phase again occurs when the predetermined discharge voltage is reached . in a corresponding fashion , a timer pulse starting a subsequent time control block is also supplied by the block t 232 . that is effected by the discharge voltage associated with the respectively ascertained time constant being ascertained from the control unit for the end of discharge as indicated at 25 , and being fed to the voltage comparator 28 through 30 associated with the respective discharge phase ( active time control block ). as soon as the current discharge voltage which is ascertained by the volt meter 26 reaches or falls below the value held in the respective voltage comparator , it delivers the control signal for terminating discharge in the respective phase . the output pulses of the time control blocks t 21 , t 22 and t 232 are combined together by way of an or - gate 31 . the output signal of that or - gate 31 serves for actuation of the subsequent time control blocks . in the normal case this is the time control block t 3 which triggers serial discharge of the two capacitors c 1 and c 2 by activation of the switching blocks s 22 , s 23 , s 31 and s 33 . that serial discharge can possibly also be omitted under certain circumstances . this is also established by the time constants determined with the group 27 . a selection block 32 determines the further discharge sequence by means of two and - gates 32 and 33 . in dependence on the output signal of the selection block which in turn is actuated by the control unit 25 for terminating discharge , the output signal of the or - gate 31 is passed either by way of the and - gate 33 to the time control block t 3 or by way of the and - gate 34 and a further or - gate 35 to the time control block t 4 . in the case of activation of the time control block t 3 the above - described serial discharge takes place while in the other situation parallel bi - phase residual discharge similarly takes by way of the time control block t 4 . in this respect the residual charge of the capacitors c 1 and c 2 is discharged after attainment of the respective end of the discharge procedure , at the threshold voltages in question , with a bi - phase voltage reversal . in this respect , the arrangement ascertains by way of the voltage comparator 30 when the output voltage at the electrodes has reached a residual voltage . that residual voltage is fixedly stored in the voltage comparator . in the other situation , more specifically when series discharge is skipped , activation of the time control block t 4 for activating bi - phase discharge is effected by way of the and - gate 34 on the basis of the corresponding output signal of the selection circuit 32 immediately after activation of one of the time control blocks t 21 , t 22 or t 232 . instead of the normalized residual voltage or the tilt , “ shut - down ” of the respective capacitor combination at the intended residual voltage can also be effected by means of a suitable time presetting which is respectively established starting from the initial voltage , on the basis of the ascertained time constant . the time control blocks shown in fig3 are then not each reset by an external control signal which marks the end of the respective period of time , but receive the remaining residual time ascertained as set forth hereinbefore , transmitted from the unit 25 . then , after expiry of the residual time , this being controlled by suitable timer means , delivery of the signal identifying the end of the respective period of time takes place for evaluation of the further control procedures towards the right in the drawing , as was described hereinbefore . the invention is not limited to the illustrated embodiments and in particular it is not bound to a configuration in just hardware or just software terms as the primary consideration is the described functionality , more specifically the described behavior of the system as a reaction to the input conditions set forth . in this respect the structure of timing members used can also serve as a starting point for the design of a suitable flowchart as a basis for control software , in which respect the procedures which are reproduced in parallelized mode only have to be edited in the manner of a flowchart with the corresponding logical links for serial processing . it therefore also immaterial whether the system is used as an implantable or external system or also as part of a larger overall system . thus the described functionality can also serve for example as an operating procedure for a system of higher order , and in particular in regard to ascertaining the respective operating parameters it is possible to make use with the same degree of success both of the respectively specified calculation methods and also look - up tables in which the stored values are each looked up and read off .
a defibrillator for atrium and / or ventricle having at least two capacitors which in the production of defibrillation pulses are discharged in at least two phases in succession in different configurations , wherein there are provided switching means which control the discharge in the at least two discharge phases in such a way that the mean value of their voltages is substantially equal and no voltages below the rheobase occur in any of the discharge phases , and a corresponding defibrillation method .