Abstract:
An electrode ( 10 ) for treating organic tissue by means of direct current, comprising an electrode holder ( 20 ), at least one electrically conductive electrode surface ( 30 ), which is let into the electrode holder ( 20 ), wherein the at least one electrode surface ( 30 ) is connected to at least one control element ( 400 ) and wherein the at least one control element ( 400 ) is connected to a control and energy supply unit by way of electrical lines ( 60, 70 ), wherein the at least one control element ( 400 ) is configured in such a way that each individual electrode surface ( 30 ) is actuable by the at least one control element ( 400 ) in such a way that a current density (J) provided within a predetermined interval for each one of the at least one electrode surfaces ( 30 ) can be maintained or that a current density (J) for each one of the at least one electrode surfaces ( 30 ) can be maintained around a predetermined value.

Description:
TECHNICAL FIELD 
       [0001]    The present invention relates to an electrode and to a method for treating organic tissue by means of direct current. 
       PRIOR ART 
       [0002]    WO 2006/106132 A1 describes an electrode for treating organic tissue by means of direct current. 
         [0003]    US 2010/152864 A1 describes an implant for use on a bone, comprising an electrical stimulation system, in which the control is suitable for limiting or controlling the current density at the implant-bone interface. 
         [0004]    WO 2007/070579 A2 describes an implant for stimulating the regeneration of damaged spinal nerves, in which a direct current is applied near the damaged sites at a level sufficient to induce regeneration, without applying a current level at which tissue toxicity occurs. 
       PRESENTATION OF THE INVENTION 
       [0005]    A problem addressed by the present invention is therefore that of improving the effect of the treatment while simultaneously increasing the safety of the treatment. 
         [0006]    This problem is solved according to the invention by electrodes having the features of claim  1  and by a method having the features of claim  14 . 
         [0007]    The electrode according to the invention for treating organic tissue by means of direct current comprises an electrode support and at least one electrically conductive electrode surface which is embedded in the electrode support, wherein the at least one electrode surface is connected to at least one control element and wherein the at least one control element is connected to a control and power supply unit by way of electric lines. 
         [0008]    The at least one control element is configured in such a way that each individual electrode surface is controllable by the at least one control element in such a way that a current density provided within a predetermined interval for each one of the at least one electrode surface can be maintained, or that a current density for each one of the at least one electrode surface can be maintained around a predetermined value. 
         [0009]    Preferably, the at least one control element is situated on the back or at the side of the at least one electrode surface. 
         [0010]    The predetermined current density on the electrode can be maintained by controlling/regulating the current or the voltage. The current density can be maintained, in particular, for a time period of several minutes up to half an hour. Subsequently, a direct current having the opposite polarity can be provided for the same time period or for a shorter or longer time period; this makes it possible to reliably prevent electrolytic residue from forming due to the current introduction. 
         [0011]    As a result of maintaining a previously set current density, it can be ensured that the current density becomes neither too high nor too low. A current density which is too high can be harmful to the organic tissue, and a current density which is too low can have a diminished therapeutic effect. 
         [0012]    Preferably, the organic tissue is cardiac tissue, preferably a heart muscle. The electrode according to the invention is situated directly at the heart muscle, the so-called epicardium, so that a conductive connection results between the heart muscle and the electrode. 
         [0013]    In one preferred embodiment, the at least one control element comprises a first control element which is designed as a constant-current source, and a second control element which establishes the voltage and the polarity at the constant-current sources. 
         [0014]    Preferably, at least one first control element is assigned to each individual electrode surface. This permits a precise control/regulation of each individual electrode, which results in a more precise maintenance of the predetermined value. 
         [0015]    Preferably, at least one second control element is assigned to all electrode surfaces jointly. The first control element is connected to the second control element by way of electric lines, wherein the second control element is advantageously situated at a distance from the at least one electrode surface. The second control element is situated close to the electrode, however, for example, in a connection area of the electrode having a supply line which includes the electric lines for controlling/regulating the current density and, optionally, further electric lines, such as, for example, a measuring line, by means of which, e.g., an EKG or an impedance can be measured, or a further control/regulating line. 
         [0016]    The second control element is situated upstream from the first control element and performs higher-order functions. For example, the current or voltage for the second control element is predetermined and the first control element operates with this predetermined operating current or this predetermined operating voltage. This structure of the first and the second control elements allows for a compact design of the individual control elements and simplifies the control/regulation of the particular current density at the particular electrode. 
         [0017]    In one advantageous embodiment, at least two electrode surfaces are embedded in one shared electrode support. The electrode support is designed so as to be integrally interconnected. Due to this arrangement of the electrode surfaces, an electrode element can be implemented, which is easy to handle and has sufficient flexibility, so that the electrode can follow the movements of the organic tissue, and a detachment of the electrode from the surface of the organic tissue can be reduced or avoided. 
         [0018]    In yet another advantageous embodiment, each of the at least two electrode surfaces, with the corresponding at least one control element, is embedded in a separate electrode support, wherein these individual electrode supports are connected to one another by means of a connection strand. An electrode designed in this way is distinguished by high flexibility. This flexibility ensures that the electrode does not detach from the surface of the organic tissue due to the movements thereof. 
         [0019]    Further embodiments comprising uniformly distributed electrode surfaces of the same size are likewise possible, for example, a circular or elliptical electrode having electrode surfaces which have the shape of a circular segment or an elliptical segment, or an annular electrode having electrode surfaces in the shape of annular segments. 
         [0020]    The number of electrode surfaces can be two to two hundred, preferably ten to one hundred. The following applies: The greater the number of electrode surfaces, i.e., the smaller the segmenting, the less likely it is that the electrode will become detached. It is likewise possible that the detachment of one single electrode surface is less significant in the case of smaller segmenting, which has an advantageous effect on the treatment. 
         [0021]    The electrode can be segmented into an even or uneven number of electrode surfaces. Alternatively, multiple rows of electrode surfaces can be situated laterally with respect to the longitudinal central axis. Circular, annular, or elliptical electrodes can likewise comprise multiple rows of concentrically situated electrode segments. 
         [0022]    Embodiments having electrode surfaces which are non-uniformly distributed and/or are not the same size are likewise possible. Areas of the electrode having smaller electrode surfaces allow for a larger curvature. Electrodes can be designed in such a way that the distribution and arrangement of the electrode surfaces are adapted to the curvatures prevailing on the surface of the heart. For example, one electrode comprises smaller electrode surfaces, which are laterally surrounded by larger electrode surfaces, along its longitudinal central axis. Alternatively, one electrode can comprise larger electrode surfaces in its central area and smaller electrode surfaces in its edge area. 
         [0023]    The electrode surfaces can be produced from thin, conductive, biocompatible materials having low polarization, for example from platinum or platinum iridium. Alternatively, the electrode surfaces can be a knitted fabric or woven fabric produced from thin, conductive, biocompatible materials having low polarization, for example from platinum or platinum iridium. 
         [0024]    The knitted-fabric or woven-fabric structure has the advantage that it can adapt very well to the underlying tissue. Such structures likewise have a certain permeability for fluids, which at least partially prevents an accumulation of fluids between the underlying tissue and the electrode surface. 
         [0025]    The knitted-fabric or woven-fabric structure promotes an at least partial adhesion with the underlying tissue, for example, with connective tissue, which improves the contact between the underlying tissue and the electrode. 
         [0026]    The knitted fabrics or the woven fabrics can be embedded in one single electrode support, in each case, or in one shared electrode support. 
         [0027]    Alternatively, the knitted fabric or the woven fabric can have alternating conductive and non-conductive areas, so that individual electrode surfaces, which are independent of one another, form an interconnected knitted fabric or woven fabric. 
         [0028]    The individual knitted-fabric or woven-fabric surfaces can be enclosed by an electrically conductive frame. Such a frame prevents the knitted fabric or woven fabric from falling apart as a result of movement. The stiffness of the frame can be influenced by the dimensions and material properties of the frame. Alternatively, the frame can also be produced from a non-conductive material. 
         [0029]    In the method according to the invention for controlling the current density (J) on an electrode according to the invention, the voltage applied at each electrode is controlled/regulated in such a way that a current density predetermined for each individual electrode surface is maintained. 
         [0030]    Preferably, the control/regulation is implemented by a MOSFET element or a bipolar transistor. These electrical components are distinguished by a compact design and ensure a reliable and exact control/regulation. 
         [0031]    In yet another embodiment, the electrode comprises at least one one-way valve which permits the drainage of fluid which accumulates under the electrode. Draining the fluid makes it possible to prevent the electrode from gradually detaching from organic tissue or it simplifies detachment. Consistently good contact between the electrode and the surface of the organic tissue is therefore ensured. 
         [0032]    Preferably, the at least one one-way valve is situated within an electrode surface. As a result, the fluid is drained at the point where it has the greatest negative influence on the contact between the electrode surface and the surface of the organic tissue. 
         [0033]    In yet another preferred exemplary embodiment, the at least one one-way valve is situated between adjacent electrode surfaces. The arrangement between adjacent electrode surfaces permits the arrangement of the at least one one-way valve in the electrode support and makes it possible to design the electrode surfaces without openings. 
         [0034]    Preferably, the at least one one-way valve is a diaphragm valve having a valve diaphragm. 
         [0035]    A method for controlling the current density (J) on an electrode according to the present invention is characterized in that the current (I) flowing through each electrode is regulated in such a way that a current density (J) provided within a predetermined interval for each individual electrode surface is maintained. Alternatively, the current density (J) is maintained around a predetermined value for each one of the at least one electrode surface. 
         [0036]    Due to the selection of a current density interval, no adjustments of the presetting of the current density are necessary in this interval. 
         [0037]    If the current density is regulated around a predetermined value, a treatment-specific current density can be set, which is particularly advantageous. 
         [0038]    Each electrode according to the invention can be used as a current-feeding or current-receiving electrode. 
         [0039]    If the control electronics are not provided on the electrode or electrodes, a series of lines would be necessary between the power supply and the electrodes; this is then at least one line per electrode, which, when several electrodes are present, results in an inflexible cable assembly. The invention provides a solution in this case, since the connection to the control and power supply unit is a two-wire connection which is used exclusively to supply current, while the control and regulation takes place by way of the control elements situated in the electrode. 
         [0040]    Further embodiments are described in the dependent claims. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0041]    Preferred embodiments of the invention are described in the following with reference to the drawings which are intended merely for the purpose of explanation and are not intended to be interpreted to be limiting. In the drawings: 
           [0042]      FIG. 1  shows a single electrode according to the invention; 
           [0043]      FIG. 2  shows a further embodiment of an electrode according to the invention; 
           [0044]      FIG. 3  shows a further embodiment of an electrode according to the invention; 
           [0045]      FIG. 4  shows an alternative embodiment of the electrode from  FIG. 1 ; 
           [0046]      FIG. 5  shows an alternative embodiment of the electrode from  FIG. 2 ; 
           [0047]      FIG. 6  shows an alternative embodiment of the electrode from  FIG. 3 ; 
           [0048]      FIG. 7  shows a schematic diagram of the control circuit; 
           [0049]      FIG. 8  shows a MOSFET control element; 
           [0050]      FIG. 9  shows a bipolar control element; 
           [0051]      FIG. 10  shows an electrode according to the invention during use; and 
           [0052]      FIG. 11  shows an electrode according to the invention comprising a one-way valve. 
       
    
    
     DESCRIPTION OF PREFERRED EMBODIMENTS 
       [0053]      FIG. 1  shows a single electrode  1  according to the invention comprising a first electrode support  2 , in which a first electrode surface  3  is embedded. The first electrode support  2  surrounds the first electrode surface around the sides and the back, at least partially, preferably completely. The electrode surface  3  is connected by way of an electric line  600  to a first control element  4  which is situated at a distance from the electrode surface  3  in a supply line  200  and which is connected by way of electric lines  60 ,  70  to a control and power supply unit  900  depicted in  FIG. 10 . The first control element  4  can be situated close to the electrode surface  3 , i.e., in the connection area having the supply line  200 , in the control and power supply unit  900 , or therebetween. The current density J of the electrode surface  3  can be controlled/regulated by means of the first control element. 
         [0054]    A non-illustrated second control element  5  (see  FIG. 5 ) can be situated together with the first control element  4 , adjacent thereto, or in the control and power supply unit  900 . 
         [0055]    An electrode surface can possibly detach from the tissue on which it preferably completely rests. If the electrode is then regulated in such a way that a constant current I flows therethrough, the current density increases when the electrode becomes detached, since the area through which the current I can flow is reduced. 
         [0056]    Given, for example, an electrode surface  3  which is 100 square centimeters in size, and a direct current I of 1 milliampere, the current density is 0.01 milliamperes per square centimeter. If the electrode surface detaches from the tissue, then only 10 square centimeters (i.e., one-tenth), for example, are still in contact, in which current can flow. If constant-current regulation were applied, the current density would increase ten-fold, to 0.1 milliamperes per square centimeter, since the area has become ten times smaller due to the detachment. Such high current densities are undesired, since they can trigger cardiac arrhythmia, for example. 
         [0057]    The electrode  1  optionally comprises at least one one-way valve  21  which essentially comprises an opening  22  and a diaphragm  23  covering the opening  22  on the outer side. A schematic sectional view of the one-way valve  21  is depicted in  FIG. 11 . The diaphragm is made from silicone, for example. The at least one one-way valve  21  is situated within the electrode surface  3 . 
         [0058]      FIG. 2  shows yet another embodiment of a segmented electrode  10  according to the invention. The electrode  10  comprises multiple electrode surfaces  30  which are separated from one another and are embedded in a shared, second electrode support  20 . 
         [0059]    All electrode surfaces  30  are of the same size and are situated in pairs, symmetrically with respect to the longitudinal central axis of the electrode. Eight electrode surfaces  30  are shown, wherein four are situated on one side of the longitudinal central axis and four are situated on the opposite side of the longitudinal central axis. 
         [0060]    The electrode support  20  comprises a border  26  which laterally encloses all electrode surfaces and comprises webs  25  which separate the individual electrode surfaces from each other, wherein the web lying on the longitudinal central axis is a central web  27  which contains the electric lines  600  which connect a control module  400  to the individual electrode surfaces  30 . The control module  400  comprises multiple control elements  4  which control/regulate the current density J in the particular electrode surface. The number of control elements  4  per control module  400  correlates with the number of electrode surfaces  30 . 
         [0061]    Electric lines  60 ,  70  connect the control module  400  to the non-illustrated control and power supply unit  900 . The second control element  5  (not shown) can be disposed in the control module  400 , adjacent thereto, or in the control and power supply unit  900 . In other words, situated between the control and power supply unit  900  and the control module  400  are electric lines  60 ,  70 , in particular, which are used for the power supply and can establish the connection to the battery provided there. 
         [0062]    In the depicted arrangement, the electrode surfaces  30  are situated opposite one another with respect to the longitudinal central axis of the electrode  10  in groups of two and form one pair of electrode surfaces in each case. Four such pairs are situated next to one another in the direction of the longitudinal central axis. 
         [0063]    The use of a plurality of electrode surfaces  30  has the advantage that, if one of the electrode surfaces  30  becomes detached, the current density J of the corresponding electrode surface can be regulated in such a way that it does not exceed an established value and the remaining electrode surfaces  30  of the segmented electrode  10  are not adversely affected thereby. 
         [0064]    The electrode  10  comprises at least one one-way valve  21 . The at least one one-way valve  21  can be situated within the webs  25 . Alternatively or additionally, said valve can be situated within an electrode surface  30 . Alternatively or additionally, said valve can be situated within the central web  27 . 
         [0065]    Alternatively or additionally, said valve can also be situated in the middle of four adjoining electrode surfaces  30 , i.e., at intersections of the webs  25  and the central web  27 . The at least one one-way valve  21  is designed in such a way that fluid which accumulates under the electrode surface  30  can reach the back side of the electrode  10  in only one direction through said electrode. 
         [0066]      FIG. 3  shows one alternative embodiment of a segmented electrode  11  according to the invention. In contrast to the previous embodiment, each of the individual electrode areas  30  is embedded in separate electrode supports  2  which are connected to one another by means of a connection strand  201 . 
         [0067]    As in the previous embodiment, a control module  400  is provided, by means of which the current density J of each electrode area  30  can be controlled/regulated. In turn, the control module  400  is connected to the non-illustrated control and power supply unit by way of electric lines  60 ,  70  which are routed in the supply line  200 . 
         [0068]    Electric lines  600  extend from the control module  400  to the particular electrode surface  30 . The electric lines  600  are routed in the connection strand  201 . The connection strand comprises lateral branches along its longitudinal direction, each one of which leads to an electrode surface  30 . 
         [0069]    The electrode  10  can comprise at least one one-way valve  21  which is situated within an electrode surface  30 . 
         [0070]    In the case of the electrode surfaces  3 , the electrodes  1 ,  10 ,  11  depicted in  FIGS. 1 to 3  are knitted fabrics or woven fabrics made of thin, conductive, biocompatible metal wires having low polarization, for example, of platinum or platinum iridium. Alternatively, thin metal foils can be used instead of the knitted fabrics or woven fabrics. 
         [0071]      FIG. 4  shows one alternative embodiment of the electrode from  FIG. 1 . In contrast to the embodiment from  FIG. 1 , the first control element  4  is situated directly on the electrode surface  3 . Electric lines  6 ,  7  are routed in the supply line  200  and are connected to the non-illustrated control and power supply unit  900 . The second control element  5  can again be situated in the first control element  4 , adjacent thereto, or in the control and power supply unit  900 . 
         [0072]    Further electric lines  8  can likewise lead up to the second electrode support  20 . Said electric lines can be measuring lines which are required for measuring the EKG or impedance. 
         [0073]      FIGS. 5 and 6  show one alternative embodiment of the electrode from  FIGS. 2 and 3 , respectively. In contrast to the embodiment from  FIGS. 2 and 3 , the first control element  4  is situated directly on the electrode surfaces  30 . The first control elements  4  of the electrode surfaces  30  are connected to one another and to the second control element  5  by way of electric lines  60 ,  70 . 
         [0074]    The electrode surfaces  3  of the electrodes  1 ,  10 ,  11  depicted in  FIGS. 4 to 6  are thin, conductive, biocompatible metal foils having low polarization, being made, for example, of platinum or platinum iridium. Alternatively, knitted fabrics or woven fabrics made of thin metal wires can be used instead of the metal foils. 
         [0075]      FIG. 7  shows a schematic diagram of the control circuit of an electrode arrangement according to the invention comprising an electrode  10  and a counterelectrode  100  of the type in use in  FIG. 10 . The control circuit comprises, for each electrode surface  30 , a first control element  4  in the form of a constant-current source, and comprises a second control element  5  which establishes the polarity of the first control elements  4 . 
         [0076]    The first control element  4  is preferably a transistor-based control element, for example, a first control element  4  having a MOSFET transistor  9  or an alternative first control element  4  having a bipolar transistor  90 . 
         [0077]    Viewing  FIG. 2  and  FIG. 7  in combination reveals the possibility of providing only the control with the first control elements  4  on the implant, on the patch electrodes, and of moving the second control with the second control elements  5  to another point, as indicated by way of the connection labeled with the reference numbers  60  and  70  which, in the exemplary embodiment according to  FIG. 2 , establish the connection to the outside, where the control and power supply unit  900  is located, i.e., in deviation from the exemplary embodiment according to  FIGS. 5 and 6 . 
         [0078]      FIG. 8  shows a schematic illustration of a MOSFET control element  40  comprising a MOSFET transistor  9 , and  FIG. 9  shows a schematic illustration of a bipolar control element  41  having a bipolar transistor  90 . 
         [0079]    The bipolar control element  41  is described in greater detail in the following with reference to  FIG. 9 . The principle of current regulation for a current direction (predefined polarity) can be implemented by means of a bipolar transistor  90 , an emitter resistor R 7 , and a reference voltage at the base of the transistor. The emitter resistor R 7  is situated at the reference potential (at the positive or negative supply voltage for the current regulator). The collector output is connected to the electrode  10  which rests flat on the heart muscle. 
         [0080]    As depicted in  FIG. 10 , the current circuit is closed via the second counterelectrode  100  lying on the opposite side of the heart. The opposite electrode is likewise provided with current regulators, in order to ensure a defined distribution of the current. 
         [0081]    Alternatively, the current circuit can be closed via the control and power supply unit  900 . In this case, only one electrode  10  is present, however. 
         [0082]    Diodes D 6 , D 7  in the collector lines provide for the intended current direction, for example, of the PNP and NPN transistors. Independently of the intended current direction, the diodes perform a protection function, in order to prevent a control of the bipolar transistors  90  along the collector-base path. 
         [0083]    Safety considerations (limitations of high frequencies) are the reason for dispensing with a Miller capacitor (negative feedback capacitor between the collector and the base), in order to prevent feedback from the electrode via the collector onto the base. The limiting of high frequencies is achieved by means of further capacitors. 
         [0084]    The voltage drop, measured across the emitter resistor R 7 , determines the constant current at each individual electrode  1  or each individual electrode segment  10 . This voltage can be changed via the control line which leads to the bases of the transistors. As a result, the setpoint current (therapy current), which is supposed to flow through the heart muscle via the corresponding electrode surface, is set. 
         [0085]    Each individual transistor automatically regulates itself via its own emitter, as a voltage probe, and thereby maintains the setpoint current which has been set, in the presence of fluctuating transistion resistances, without feedback loops to the control and power supply unit. 
         [0086]    The automatic regulating range (change in internal resistance of the transistor) is multiple times larger than the adjustment range via the control voltage. 
         [0087]    On the basis of the control voltage between the main line and the base, minus the base emitter voltage U BE  of approximately 0.6 volt which drops across the base-emitter path, the constant current can be calculated according to Ohm&#39;s law: 
         [0000]      ( U−U   BE )/ R=I    
         [0000]      wherein U BE =0.6 volt 
         [0088]    Since the desired current lies in the μampere range, 0.6 volt should be taken into account, instead of 0.7 volt which is typical. 
         [0089]    The emitter resistor R 7  should have a size of 20-100 kiloohms, depending on the number of desired electrode segments and the current range which is used. 
         [0090]    For medical reasons and due to electrochemical effects, the current direction should be changeable (change the polarity). For this reason, a second transistor (NPN-PNP) having a diode is required in the collector line. 
         [0091]    For the particular other current direction, the polarity of the lines to the electrodes can be switched electronically in the control and power supply unit. This applies for the line for the control voltage just as it does for the lines for the therapy current. 
         [0092]    In order to switch off the therapy current, the voltage can be lowered to below a threshold of 0.4 volt at at least one of the two control lines. For safety reasons, in addition to lowering the voltage below the aforementioned limit of 0.4 volt, it is provided that the corresponding analog switch is switched to high impedance. For this reason, analog switches having 3 connectors cannot be used. 
         [0093]    The resistor R 6  has relevance for the case in which the surface element of the electrode has a high resistance to the heart muscle (loss of contact). In this case, the regulating transistor would attempt to draw the missing current across the base. The resistor (R 6 , approximately 50-150 kiloohms) limits the lost current to tolerable values. In such a configuration, the resistor R 6  is connected in series to the resistor R 7 . 
         [0094]    The current loss which sets in can be calculated from the control current minus U BE  0.6 volt divided by (R 6 +R 7 ). 
         [0095]    In normal operation (good contact of the electrode to the heart muscle), the largest portion of the therapy current flows across the collector and only a minimal residual current flows across the base. In the case of amplification factors of 100 to 300, the size of the residual current is only approximately 1 to 0.33 percent of the therapy current. 
         [0096]    The resistor R 5  [100-500 ohms] has the function of a protective resistor and, together with the diode D 8  [two 12-14 volt zener diodes connected back to back], forms a bidirectional overvoltage protection D 8 . The voltage for the zener diodes is selected to be so high because the zener diodes have a substantially lower leakage current starting at approximately 10-12 volts. 
         [0097]    This not only has to do with static discharges which should be dissipated, but also with an effective protection against the defibrillator pulse having an amplitude of up to 1500 volts for 10 milliseconds (25 amperes). Therefore, the resistor must withstand impulse voltages of 1500 volts. 
         [0098]    Capacitors C 5 , C 6  are provided for protection against incident high frequency and against the inherent tendency to oscillate. The regulating transistor, by way of its stepless analog regulating task, can find a working point at which it starts to oscillate. 
         [0099]    The capacitors are dimensioned in such a way that the correction time does not adversely affect the function. A proven standard value is 100 nanofarads for C 6  and 10 nanofarads for C 5 , if the size of the capacitors does not play a role. In the present application within the electrode, values of 10 nanofarads (dielectric strength 10 volts) for C 6  and of 5 nanofarads (voltage strength 20 volts) for C 5  are also acceptable. It is permissible for the capacitance to deviate greatly upward in the event of a temperature change, but the indicated capacitance must not be fallen below. 
         [0100]    Given a predefined overall surface area F of 6×8 centimeters, an area F of 48 square centimeters results. In the case of a setpoint current density J, for example, of 0.001 milliamperes per square centimeter, a required current I of 0.048 milliamperes results. 
         [0101]    For 12 individual surfaces N, for example, wherein each surface has 4 square centimeters, this means that each surface has a maximum current I of 0.004 milliamperes which may be given off, as the maximum, as therapy current. 
         [0102]    A value R of 40 kiloohms results for R 7 . The control voltage is calculated as follows: 
         [0000]        R/N= 3.33 kiloohms× I= 0.16 volt= U,  
 
         [0000]      wherein R=40 kiloohms, N=12, I=0.048 milliamperes 
         [0000]        U+u= 0.16+0.6=0.76 volt= U   max    
         [0000]      wherein u=0.6 volt (voltage drop) 
         [0103]    A maximum control voltage of 0.76 volt must be available in parallel for all 12 current regulators for a multisensor electrode having 12 surfaces. 
         [0104]    The setpoint current density can be maintained in an interval of 0.1 to 20 milliamperes per square centimeter, preferably between 1 to 15 microamperes per square centimeter, preferably between 5 and 10 microamperes per square centimeter. Alternatively, the current density J can be maintained around a value contained in the aforementioned intervals. For example, the current density can be maintained around 10 microamperes per square centimeter. 
         [0105]    If a MOSFET transistor  9  is used instead of a bipolar transistor  90 , as depicted in  FIG. 8 , the threshold voltage increases relative to the control voltage to approximately 0.8 volt (this is the gate voltage at which MOSFETs just start to conduct), and a voltage drop of 0.25 volt occurs across the Schottky diodes D 4 , D 5  situated in front of the gate. This results in a threshold voltage of 1.05 volts relative to the control line. 
         [0106]    The temperature behavior of the diodes counteracts the temperature behavior of the MOSFETs. MOSFETs  9 , in contrast to bipolar transistors  90 , become higher-impedance when heated. 
         [0107]    The primary task of the diodes D 4 , D 5  is to prevent a discharge current across the internal protective diodes of the MOSFETs. Only 2 diodes are required for all current regulators. The gates of the P-channel MOSFETs can also be connected directly in parallel, as is the case with all N-channel MOSFETs. 
         [0108]    The resistors R 2 , R 4  (1 megaohm each) are high-impedance and are intended to ensure a reliable blockage of the MOSFETs. This is necessary due to the diodes. Two resistors are sufficient for all individual areas of the multi-area electrode. 
         [0109]    The capacitors C 3 , C 4 , as is also the case with the capacitors C 1 , C 2 , are provided as protection against incident high frequency and against the tendency to oscillate (no difference from the circuit having the bipolar transistors). In this case as well, two capacitors C 3 , C 4  suffice for all individual surfaces. While C 3  and C 4  are sufficient for all current regulators, the capacitors C 1  and C 2  should be provided in each current-regulating circuit. 
         [0110]      FIG. 10  shows an electrode  10  according to the invention in use, wherein said electrode is situated on a first outer surface of the heart H of a patient P, and a counterelectrode  100  is situated on a second outer surface of the heart H, which is essentially opposite the first side. Preferably, the electrode  10 , essentially, and the counterelectrode  100  are situated on a front and a rear surface, respectively, of the heart. Alternatively, the electrodes can also be situated on a left- or right-oriented surface of the heart. The advantage of these arrangements is that the current flows substantially through the heart or through the heart muscle. 
         [0111]    The counterelectrode  100  can be designed identical to or substantially identical to the opposite electrode  10 . Said electrode can also have a different distribution or segmentation of the electrode surfaces. 
         [0112]    Supply lines  200  extend from the electrodes  10 , from each electrode  10 ,  100  to a shared control and power supply unit  900  which, for example, comprises a generator and receiving unit, a telemetry unit, and a power supply unit. 
         [0113]    An electrode according to the invention makes it possible to improve the effect of the treatment while simultaneously increasing the safety of the treatment. 
       LIST OF REFERENCE NUMBERS 
       [0000]    
       
           1  individual electrode 
           10  segmented electrode 
           100  counterelectrode 
           11  alternative segmented electrode 
           2  first electrode support 
           20  second electrode support 
           200  supply line 
           201  connection strand 
           21  one-way valve 
           22  opening 
           23  diaphragm 
           25  web 
           26  border 
           27  central web 
           3  first electrode surface 
           30  second electrode surface 
           4  first control element 
           40  MOSFET control element 
           400  control module 
           41  bipolar control element 
           5  second control element 
           6 - 8  electric line 
           9  MOSFET transistor 
           90  bipolar transistor 
           900  control and power supply unit 
         R 1 -R 7  resistor 
         D 1 -D 8  diode 
         C 1 -C 6  capacitor 
         I current 
         J current density 
         U voltage 
         P patient 
         H heart