Patent Publication Number: US-2023149707-A1

Title: A process for treatment of internal organ oedema using an electric current delivering electrode system and system therefor

Description:
TECHNICAL BACKGROUND 
     Technical Field 
     The present invention relates to a process of treatment of internal organ oedema using an electrical current delivering electrode system comprising two electrodes to be positioned at two places on or close to the internal organ or in liquid carrying vessels as part of the organ or in the internal organ as well as a device for the reduction up to removal outside of internal organ oedema and a system, therefor. 
     TECHNICAL CONSIDERATIONS 
     Primary or secondary disease of an organ, acute or chronic infections or a reduced blood supply to organs are often associated with oedema of the affected organ, which can severely impair the function of the organ. In the heart, this is particularly evident in the form of a restriction of the pumping function, which has an effect on all organs of the body. Thus, internal organ oedema relate to myocardial oedema as described in the following prior art articles but also to kidney oedema or liver oedema to name specific internal organs. Reduced pumping function of the heart typically leads to a congestion of blood in other dependent organs (e.g. liver, kidney), which impresses as oedema in these organs. The extent of the oedema in these organs depends on the severity of the heart dysfunction. Organ oedema can also occur independently of a reduced pumping function of the heart in organ-specific diseases (e.g. diseases of the kidney or liver), such as nephrotic syndrome or inflammation of the liver. 
     The article “Myocardial Edema on T2-Weighted MRI—New Marker of Ischemia Reperfusion Injury and Adverse Myocardial Remodeling” by Yuko Tada and Phillip C. Yang in http://circres.ahajournals.org DOI: 10.1161/CIRCRESAHA.117.311494; identifies myocardial oedema as problematic within myocardial infarction patients and suggests new marker therefor. No specific treatment is mentioned. 
     The article “Why Edema Is a Matter of the Heart” by Matthias G. Friedrich, in http://circimaging.ahajournals.org DOI: 10.1161/CIRCIMAGING.117.006062 explains the important relationship between myocardial oedema and myocardial infarction and the possibility to differentiate between acute and remote myocardial infarction based on oedema-sensitive CMR (for cardiac magnetic resonance). 
     In the European Journal of Heart Failure, vol. 2018, edited by the European Society of Cardiology, Thomas M. Gorter answered in a letter to the editor “Myocardial oedema and congestive heart failure: one piece of the puzzle? Reply” on pp827-828, myocardial oedema is mentioned to be an interesting topic for research in view of the link with heart failure. 
     In “Global myocardial oedema in advanced decompensated heart failure” by Frederik H. Verbrugge et al. in European Heart Journal—Cardiovascular Imaging (2017) 18, pp787-794 doi:10.1093/ehjci/jew131 it is disclosed that cardiac magnetic resonance (CMR) imaging with quantitative T2 mapping can be used to identify myocardial water content in patients and evaluate the change with decongestive therapy. 
     Ranjeet M. Dongaonkar et al. shows in “Myocardial microvascular permeability, interstitial oedema, and compromised cardiac function” in Cardiovascular Research (2010) 87, pp331-339 doi:10.1093/cvr/cvq145 the relevance of myocardial oedema as common pathology within instability of the heart. It stipulates that the resolution of myocardial oedema does not restore normal cardiac function. The resolution of myocardial oedema with cardioplegia by avoiding systemic haemodilution is reported. 
     Maekawa H, Toda G.  Nihon Rinsho . (2005; 63(1):80-84) have described the negative impact of the storage of water (edema) in the liver for liver function. 
     In the same way Siddall EC and Radhakrishnan J. (The pathophysiology of edema formation in the nephrotic syndrome.  Kidney Int.  2012; 82(6):635-642. doi:10.1038/ki.2012.180) describe the importance of an oedema in the kidney, as it occurs in the nephrotic syndrome. 
     SUMMARY OF THE INVENTION 
     Based on the above mentioned prior art documents, it can be seen that several methods are applied to correctly identify myocardial oedema but beside the use of cardioplegia by avoiding systemic haemodilution, no treatments are disclosed in the prior art. Therefore, it is an object of the present invention to provide a process which is capable to reduce internal organ oedema and especially myocardial oedema with quite simple means. Astonishingly, it has been found that application of electrical current as such, especially DC current, between two electrodes provided on an internal organ or in liquid carrying vessels in the internal organ over hours immediately starts to reduce the swelling (oedema) and further beneficial results appear if the current application is maintained up to days, weeks or even long-term (chronically). 
     A liquid carrying vessel can be a blood vessel or a vessel of the lymphatic system or one of the two main cavities (right or left ventricular cavity) of the heart. 
     When the process is used to reduce myocardial oedema, then the electrodes are positioned on or near by or in the heart at positions taken from the group comprising inside the right ventricle, inside the coronary sinus, on the outside of the left ventricle and/or on the outside of the right ventricle. Regardless of where the electrodes are placed (for example even subcutaneously or outside the human body), it is only relevant that the current flows through the affected organ. 
     When two outside mounted electrodes are used, these can be flat electrodes (so called patch electrodes); when an outside mounted electrode is connected with an inside mounted electrode these can be realized as a flat electrode and a coil electrode, respectively. If two inside mounted electrodes are used, they usually are coil electrodes. Then the volume of the treated organ, i.e. the region where the current passes, is usually smaller than if at least one flat electrode is used. The electrode according to the invention for reducing oedema of internal organs through application of an electrical current, e.g. a direct current, comprises an electrode support and at least one electrically conductive electrode surface which is embedded in the electrode support, wherein the electrode surface is connected to a control and power supply unit by way of electric lines. 
     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 starting from several minutes up to days, i.e. longer than 24 hours. Subsequently, it is possible but not necessary to provide a direct current having the opposite polarity. 
     In both cases the direct current application provides electro-osmosis or an osmotic like effect which generates the secretion of water droplets usually at the cathode, however, depending on the composition of the liquid (electrical charge carriers in the liquid) to be removed, the liquid can also be secreted at the anode. The electroosmosis or electroosmosis-like effect can also affect the lymphatic system in the sense that increased lymph is drained from the organ tissues (interstitium) via the lymphatic system, thus reducing oedema. 
     In the case of patch electrodes, it is possible to provide a one-way valve within the patch surface, preferably surrounded by the 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. 
     Preferably, such a one-way valve is a diaphragm valve having a valve diaphragm. 
     The process of reduction of the internal oedema applies steps for controlling the current density (J) on the electrode according to the present invention wherein the current (I) flowing through the electrode is regulated in such a way that a current density (J) provided within a predetermined interval for the electrode surface is maintained. Alternatively, the current density (J) is maintained around a predetermined value for the electrode surface. 
     Due to the selection of a current density interval, no adjustments of the presetting of the current density are necessary in this interval. 
     If the current density is regulated around a predetermined value, a treatment-specific current density can be set, which is particularly advantageous since providing a predetermined electroosmotic effect. 
     In case of segmented electrodes, e.g. that different parts of a coil electrode are electrically separated one from another or that a flat electrode is separated into to electrically separated electrode surfaces, a control unit can achieve that the current density on each electrode part is maintained in such a predetermined interval. 
     Each electrode according to the invention can be used as a current-feeding or current-receiving electrode, wherein the cathode is the electrode where the maximum water is gathered and conducted away. Therefore, an important reduction effect of the internal oedema happens where the anode provides the water-reduced area. 
     The process of treatment of internal organ oedema can comprise different current delivering electrode systems. The always comprise two electrodes and a control unit. The two electrodes are to be positioned at two places in relation to the internal organ to be treated and the electrodes are connected to the control unit. The control unit is then adapted to deliver an electric current to induce electro-osmosis. 
     In one embodiment there are provided two patch electrodes, which can be one-surface electrodes or comprises a plurality of separated segments. Then the patch electrodes are mounted on the outer surface of the internal organ, which can be heart, kidney or liver. Mounted can comprise positioning or attaching. It is also possible to position the patch electrodes just subcutaneously or on the outside of the skin of the patient. 
     According to one embodiment of the present invention, the electrodes are positioned extracorporally, preferably in physical contact to the skin of a patient. Within the present invention, a place on the outer surface of an internal organ may also include a place on the external skin surface and/or the outer surface of an internal organ may include the external skin surface. 
     In addition to the aforementioned conditions, myocardial oedema plays a crucial role in the further course of the disease in patients with fresh myocardial infarction or acute myocarditis. A myocardial infarction or myocarditis that cannot be controlled because of myocardial oedema has an increased likelihood of fatal consequences. 
     Since under acute conditions it is not possible to apply the electrodes directly to an affected internal organ, as this would require a surgical intervention, albeit a minor one, electrodes are envisaged herein that apply the current with its inherent field or the electric field transdermally (with physical contact to the skin). 
     It is clear to the skilled person that electrodes which are to be positioned extracorporally are structurally different to electrodes to be positioned on internal (intracorporal) organs. Thus, according to one preferred embodiment of the present invention, the electrodes of the present invention and/or the electrode assembly system of the present invention are adapted to allow an extracorporal application thereof. Generally, the size of the electrodes of the present invention may be selected depending on the size of the person to be treated. In a preferred embodiment, the electrodes to be applied extracorporally are patch electrodes. 
     For any use according to the invention, and in particular for an external or extracorporal use or application of the electrodes according to the present invention, patch electrodes having a size in the range of from 2 by 2 cm (for babies or infants) up to 30 by 40 cm (for adults), and/or a surface area of from 4 cm 2  to 1200 cm 2 , or any size or surface area in between may be employed. Also, electrodes of different shapes or forms may be used, comprising round, elliptical, square, rectangular and freeform. 
     In one embodiment of the present invention, the electrodes contacting the skin are electrically conductive allowing electrical current to flow. In one embodiment of the present invention, at least one or all electrodes contacting the skin is/are electrically insulated allowing an electrical field to be generated without any current flow. 
     To ensure a good transition between the skin and the electrode with as little energy loss as possible, a gel or other liquid with high conductivity may be applied between the extracorporally applied electrode and the skin, similar to substances used for external defibrillation. 
     Since anti-edematous therapy may require a longer duration of application of the electrodes, one embodiment of the present invention features adhesive electrodes which may be reversibly and directly fixed to the skin surface, preferably wherein the adhesive itself has a favorable resistance behavior. Preferably, the electrically conductive surface of the extracorporal electrode(s) is designed to be deformable so that the electrode(s) can adapt to the body contours. 
     Generally, the electrically conductive electrode surface may be connected via an electrical energy conducting cable to a device that can generate and deliver the corresponding currents and voltages. 
     In another embodiment a patch electrode is combined with a coil electrode, wherein the patch electrode is positioned on the outer surface of the internal organ, wherein the coil electrode is positioned in a liquid carrying vessel of the internal organ. Then the current is flowing through the organ between the electrode in the blood or lymphatic duct vessel and the outside of the organ. 
     When the internal organ is the heart, the patch electrode is positioned for the heart on the epicardial side of the heart and wherein the coil electrode is positioned for the heart inside the ventricular cavity. 
     When the internal organ is the kidney, the patch electrode is positioned for the kidney on the outer side opposite to the renal artery and renal vein and wherein the coil electrode is positioned inside the renal artery and renal vein or the renal pelvis. 
     Finally, a process of treatment of internal organ oedema can also use two coil electrodes, wherein the two coil electrodes are positioned in different liquid carrying vessels within the same internal organ. Then the current flow is restricted between the core parts of the organ where the coil electrodes are positioned. 
     Within this embodiment in an application for the heart, one of the two coil electrodes can be placed in the coronary sinus and the other of the two electrodes can be positioned in the right or left ventricular cavity. 
     As mentioned above, the internal organ oedema to be treated can be a myocardial oedema or an oedema of the kidney or an oedema of the liver. 
     The electro-osmosis is generated for a reduction up to a removal of the internal organ oedema. 
     The electroosmotic effect comprises an accumulation of oedema fluid at the electrodes to be carried away from the electrodes. Additionally, said electroosmotic effect is to drain an accumulation of oedema fluid from the tissue (interstitium) of an organ by stimulating the lymphatic system of the corresponding organ to more rapidly remove the accumulated oedema fluid. 
     The current delivered to the electrodes and flowing through the organ can be preferably a direct current. The direct current can be an amplitude modulated direct current, i.e. a direct current wherein the intensity of current is modulated around an average value. 
     The control unit can be configured to switch the polarity of the direct current in predetermined time intervals. Such predetermined time intervals can comprise intervals between 1 hour and 7 days. The entire process can comprise a treatment time of several days up to several months. 
     It is noted that an electric current flowing between two electrodes is accompanied by electrolysis generating a pH shift in the area of the interface between electrode conducting surface and tissue and creation of gas. Since the current density is small and the electrodes are preferably made of platinum or a platinum iridium alloy (or another metal from the electrochemical series with high positive electrical voltage), the effects are limited. It is even so that the shift of the pH towards alkaline can have a beneficial effect on the tissue as inflamed tissue often has a pathological (acid) pH value. The gas generation is effected at the anode which is preferably in the flowing blood (in the blood vessel). The liquid is capable to dissolve the gas. The generated gas is especially Cl 2  which—immediately after its formation, forms bonds that are physiological and therefore harmless. The existence of an electrolysis effect, even if small, is a difference between any application of AC currents to internal organs. 
     The invention further comprises an electrode assembly comprising two electrodes and a control circuit, wherein the first and second electrodes are electrically connected to the control circuit, wherein the control unit is adapted to establish a direct current flow between the first and the second electrode. 
     The electrode assembly has preferably a control unit being adapted to switch the polarity of the current flow between the first and second electrodes. 
     The electrode assembly can comprise two patch electrodes to be positioned opposite one the other of the internal organ so that the current flow between the first and second electrodes is traversing the internal organ. 
     The electrode assembly can have a mixed lay-out with one coil electrode and a patch electrode, wherein the coil electrode is to be positioned inside a liquid vessel of the internal organ and the patch electrode is to be positioned outside of the internal organ so that the current flow between the first and second electrodes is traversing the internal organ oedema part. 
     The electrode assembly can have two coil electrodes to be positioned both inside in different liquid vessels of the internal organ so that the electric current flow between the first and second electrode is traversing through the internal organ oedema part especially between the two liquid vessels. 
     The control unit of the electrode assembly can be adapted to control the strength of the current flowing between the first and second electrodes to control the strength of the electric current flow through the place of the internal organ oedema over time. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Preferred embodiments of the invention are described in the following with reference to the drawings, which are for the purpose of illustrating the present preferred embodiments of a device to execute the process according to the invention and not for the purpose of limiting the same. In the drawings, 
         FIG.  1    shows a two internal electrode disposition (two internal coil electrodes) of electrodes in the heart as internal organ; 
         FIG.  2    shows a mixed (one internal coil electrode, one external patch electrode) disposition of electrodes in and outside the heart; 
         FIG.  3    shows a two external electrodes (external patches with segmented electrodes) disposition of electrodes on external heart surfaces according to the invention during use; 
         FIG.  4    shows an electrode according to the invention comprising a one-way valve; 
         FIG.  5    shows a two external electrodes (external patches with single electrodes) disposition of electrodes on external kidney surfaces according to the invention during use; and 
         FIG.  6    shows a mixed (one internal coil electrode, one external patch electrode) disposition of electrodes in and outside the kidney. 
     
    
    
     DESCRIPTION OF PREFERRED EMBODIMENTS 
       FIG.  1    shows a schematic representation of a heart  10  with an electrode assembly  20  according to a first illustrative embodiment of the invention. The implantable direct-current electrode assembly  20  comprises two implantable electrodes  30  and  40  and a control circuit  50 , usually arranged in a separate housing in which the battery for the power supply is likewise provided. 
     The two electrodes  30  and  40  are connected to the control circuit  50  via two single-conductor cables  51  and  52 . 
     The control circuit  50  is designed to establish a potential difference between the two electrodes  30  and  40 , such that a direct current can flow between these electrodes  30  and  40 . 
     One electrode  30  is a ventricular electrode, provided for positioning in the right ventricle, and is designed as a coil electrode. It is therefore designated below as a ventricular coil electrode  30 . The length of the ventricular coil electrode  30 , defined by the one conductive metallic sheath surface or coil surface defining a sheath, is ca. 4 to 10 centimeters and is designed to fill as far as possible the entire length of the right ventricle after passage through the right cardiac tricuspid valve. Here, the ventricular coil electrode  30  is placed loosely into the right ventricle, but it can touch the wall of the right ventricle. To prevent the electrode from falling into the outflow tract of the right ventricle (pulmonary valve), it is anchored actively (by screw) with its tip or passively with barbs in the tip of the right ventricle which hook into the trabecular meshwork of the right ventricle and thus fix the electrode tip. 
     From  FIGS.  1  and  2   , the electrode  30  seems to float freely in the right ventricle. However, this is only apparently the case, because the figures are schematic two-dimensional depictions. Generally, the electrode  30  will nestle on the wall of the ventricle; in the depiction in  FIG.  2   , this could be the posterior wall, which is not visible there. The electrode  30  is flexible in order to adopt these gentle curvatures, which amount to less than 30 degrees with respect to the longitudinal axis. 
     The other electrode  40  of  FIG.  1    is a coronary sinus electrode, provided for positioning in the coronary sinus, and is likewise designed as a coil electrode. This coronary sinus coil electrode  40  has a smaller diameter than the ventricular coil electrode  30  since it is intended to be advanced far into the coronary sinus in order then to come to lie in the narrowing end region there. This electrode thus lies at a position substantially predefined by the vessel walls, which position the operating surgeon otherwise establishes by advancing it in the longitudinal direction. 
     When the two electrodes  30  and  40  are subjected to a potential difference by the control circuit  50  via the attachment wires or cables  51 ,  52  insulated from the environment, a direct current then flows according to the arrow  55  through the myocardium. In a manner predetermined by the control circuit, the electrode  30  can be the cathode for a predetermined time of between a few minutes and up to chronically, whereby the direction of the current is predefined. The control circuit can then change the direction of the current after a correspondingly predetermined time, whereby the electrode  40  becomes the cathode. The current strength can also change, since the resistance between the two electrodes  30  and  40  is dependent on the direction of the current. In a further illustrative embodiment, the control device controls the current strength at a uniform predetermined value. The DC current can have a constant value or can be amplitude modulated with a modulation height of e.g. +−10% to +−25% of the average DC value. 
       FIG.  2    shows a schematic representation of a heart  10  with an electrode assembly  120  according to a second illustrative embodiment of the invention. The implantable direct-current electrode assembly  120  comprises two implantable electrodes  30  and  140  and also a control circuit  50 . 
     Identical features are provided with identical reference signs, similar features with correspondingly similar reference signs. 
     The control circuit  50  can be designed in the same way as described in  FIG.  1   . The two electrodes  30  and  140  are also connected to the control circuit  50  via two single-conductor cables  51  and  52 . 
     The control circuit  50  is also designed here to establish a potential difference between the two electrodes  30  and  140 , such that a direct current can flow between these electrodes  30  and  140  for a predetermined time of several minutes, e.g. 5 minutes, to several days, e.g. 3 days or even chronically. 
     One electrode  30  is once again a ventricular electrode, provided for positioning in the right ventricle, and is designed as a coil electrode. It is therefore also designated here as a ventricular coil electrode  30 . The length of the ventricular coil electrode  30 , defined by the one conductive metallic sheath surface or coil surface defining a sheath, is ca. 4 to 10 centimeters and is designed to fill as far as possible the entire length of the right ventricle in the longitudinal axis after passage through the right cardiac valve (tricuspid valve). Here, the ventricular coil electrode  30  is placed loosely into the right ventricle, is passively anchored at the distal end and can bear on the wall of the ventricle or on the septum. To prevent the electrode from falling into the outflow tract of the right ventricle (pulmonary valve), it is anchored actively (by screw) with its tip or passively with barbs in the tip of the right ventricle. 
     The other electrode  140  is a surface electrode (patch electrode), provided for positioning on the epicardium, the pericardium or close to the epicardium (e. g. even subcutaneously). It can be designed, for example, according to the teaching of US 2008/0195163 A1. This surface electrode  140  is applied to the left side of the myocardium, epicardially opposite the right ventricle. 
     When the two electrodes  30  and  140  are subjected to a potential difference by the control circuit  50  via the attachment wires or cables  51 ,  52  insulated from the environment, a direct current then flows according to the arrows  155  through the myocardium. This flow of current is symbolized here by two arrows which essentially show the approximate current flow direction, since the flow of current here fans out from a substantially longitudinally dimensional face of the substantially longitudinally oriented surface of the coil electrode  30  toward the surface electrode  140  and thus sweeps across a fan. Seen physically, the direct current flows through a prism; that is to say proceeding from an edge (of the prism) to its base on the patch electrode. 
     A prism is by definition a geometric body whose side edges are parallel and of equal length and which has a polygon as base. It arises from parallel displacement of a plane polygon along a straight line not lying in this plane and is therefore a special polyhedron. Here, the straight line is predefined by the longitudinal axis of the coil electrode  30 , and the polygon is a triangle with the apex at the coil electrode  30  and with a base that corresponds to the width of the surface electrode (patch electrode)  140 . If these side edges  141  of the surface electrode  140  do not come to lie parallel to the orientation of the coil electrode, it is a rotated prism. In all cases, the two electrodes  30  and  140  define a not inconsiderable spatial body which guarantees that the direct current emitted by the control circuit  50  flows through a likewise not inconsiderable sub region of the left cardiac muscle and to a slightly lesser extent also of the right cardiac muscle. Describing the geometry of the body through which the current flows as a prism is an approximation, since it can be assumed from this that the electrode does not float freely but is instead passively fixed at its distal tip and then bears on the wall of the ventricle. The boundary lines of the body are then certainly not straight but curved, and the defined body is then obtained only approximately as a prism. Of importance, however, is the narrow “edge” on the one side formed by the coil electrode, and the “broad bottom face” on the other side which is formed by the patch electrode. 
       FIG.  3    shows two patch electrodes  240  and  340  which are connected with lines  51  and  52  to a control and power supply unit  50 . Here, each patch electrode  240  and  340  as such is a segmented electrode  240  or  340 . This means, each electrode  240  or  340  is or comprises a plurality of electrode segments  241  or  341  which are shown as smaller rectangles in  FIG.  3   . Given, for example, an electrode surface of a patch electrode  240  or  340  which is 100 square centimeters in size in total, and a direct current I of 1 milliampere, the current density is 0.01 milliamperes per square centimeter. If the electrode surface (here a plurality of the electrode segments  241  or  341  detaches from the tissue, e.g. 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, and are therefore preferably controlled in control unit  50 . Therefore, usually, current densities between 0.1 to 100 microampere per square centimeter are applied, preferable 1 to 10 microampere per square centimeter. 
     Although the organ  10  can be a heart, it is also possible that the organ  10  is a kidney with applied electrodes  240  and  340 . In other embodiments it could be a liver. 
     The electrode  1  optionally comprises at least one one-way valve  70  which essentially comprises an opening  72  and a diaphragm  73  covering the opening  72  on the far side of the internal organ. A schematic sectional view of the one-way valve  70  is depicted in  FIG.  4   . The diaphragm is made from silicone, for example. The one-way valve  70  is situated within the electrode surface  75 . 
     The apparatus as described in connection with  FIG.  1 ,  2  or  3    delivers an electric current, e.g. a direct current, to the internal organ, here the heart. This electric current, e.g. a direct current, acts immediately or at least extremely fast on the internal organ, here the heart. 
     Extremely fast means that the first signs of improvement starts to appear within minutes after the current begins to flow. Irrespective of the fact that the patient describes a better feeling of well-being, echocardiography can be used to objectify a reduction in the size of the ventricle very quickly as the first positive sign. In this short period of time, this immediate improvement cannot be explained by molecular biological processes in the heart musculature; the improvement is due to electro-osmosis, a process by which water is transported osmotically (used, for example, to dry damp walls or in cosmetics). 
     It can be assumed that diseased organs are always also inflamed organs and inflammation is always associated with oedema. In relation to the heart, this means that there is an intra- and/or extracellular excess of fluid (oedema), which causes the heart muscles to swell and limits their pumping function. By applying an electric field or voltage, an osmotic like effect is induced, by which water is extracted from the heart muscles, which was before enlarged and bloated by oedema. This effect is transferable to other internal organs in which the intra- and/or extracellular excess of fluid (Oedema) leads to restricted cell function and thus reduces organ function as a whole. 
     This function is based on the insight, that the human body is a so-called ion conductor. The electric current mainly causes ion movement (electrokinesis), i.e. the migration of negatively charged anions (e.g. Cl−, CO 2 −etc.) to the anode and of positively charged cations (e.g. Na+. Mg++.etc.) to the cathode. Electro-chemical reactions occur on metals (electrodes, but also metallic foreign bodies). A migration of protein fractions (electrophoresis) and a shift of water in the direction of the cathode (electro-osmosis) takes place in the applied direct current field. In addition, the electroosmosis or electroosmosis-like effect induced by the applied current field supports and enhances drainage through the lymphatic system. The effect is as such independent from the application with two internal coil electrodes, one coil electrode and one patch electrode or two patch electrodes applied on opposite parts of the internal organ like the on the left and the right ventricle. 
     Especially in the case of direct currents, there is the theoretical risk of undesirable burns. Within the application of currents with densities in the range of 0.01 to 0.1 milliamperes per square centimeter (which is in the range that can be find in the human body physiologically), the effect of electro-osmosis can be maintained chronically without changing the polarity to enhance the water draining effect on the treated organ. Within the context of the present invention, “water” is mentioned solely as an example for the aqueous solution(s) present within the body and may be replaced by the term “aqueous solution” wherever appropriate. 
     This can be achieved with electrodes in the blood vessel system or outside of the organ in question. 
     Although the drawings only show the heart in the application, similar coil electrodes can be used for the treatment of a liver and/or a kidney. This can be used in blood vessels or the lymphatic system. Flat electrodes can be positioned on or near the liver or kidney with the flat electrodes on mainly opposite sides of the organ, so that the current passes through the organ. This can also be done subcutaneously or from the exterior of the human body. 
     As an example of the clinical success of the above described effects achieved by directly controlling an electric field applied onto the oedema-afflicted organs or vessels, the following results have been reported (Kosevic, D et al. (2021). Cardio-microcurrent device for chronic heart failure: first-in-human clinical study. ESC heart failure. 10.1002/ehf2.13242). 
     The average of patients included in the study reported therein is a New York Heart Association (NYHA) Class III non-ischemic patient in the age group of 29 to 67 years, with a body mass index of 22.5 to 35.9 and a history of heart failure, and in particular with a significantly reduced left ventricular ejection fraction (LVEF) and a 6 minute walk under about 250 m. The “6 min walk test” or “6MWT” has been developed by the American Thoracic Society as a reliable indicator in the form of a sub-maximal exercise test for assessing aerobic capacity and endurance, wherein the walking distance covered over a time of 6 minutes by the patient is used as the outcome by which to compare changes in performance capacity. Here, the average patient (as described before) achieved between ˜170 and ˜250 m at hospitalization, between ˜350 and ˜450 m after 14 days, and between ˜370 and ˜470 m after 6 months of device use, and, furthermore, the average patient&#39;s classification according to the NYHA improved to a significantly less critical class after this time period. 
       FIG.  5    shows a two external electrodes (external patches with single electrodes) disposition of electrodes on external kidney surfaces according to the invention during use. There are two kidneys  11  with a symbolic central aorta or vena renalis  13 . Ureters  12  connect the kidneys  11  with the bladder of the person. A patch electrode  440  is positioned on the outside of one kidney  11 . A second patch electrode  440 ′ (with an identical outlay to the first patch electrode  440 ) is positioned on the opposite side of the kidney  11 . Therefore, the core part of the kidney with its renal pyramids  17 , renal calix  16  and the renal pelvis  18  is positioned between the two patches  440  and patches  440 ′. 
     The flat electrode patches  440  and  440 ′ are connected with a control unit  50 , not shown in  FIG.  5   , via connection lines  51  and  52 , respectively. The supply lines  51  and  52  provide a current flow between the flat electrode patches  440  and  440 ′ which current then effectively flows through the mentioned parts of the kidney to reduce the oedema through electro osmotic effects. The electrode patches  440  and  440 ′ are shown as single electrodes but can also be segmented electrodes as shown in  FIG.  3   . 
       FIG.  6    shows a mixed (one internal coil electrode, one external patch electrode) disposition of electrodes in and outside the kidney. The kidney  11  is shown with its renal pyramids  17 , renal calix  16  and the renal pelvis  18 . The aorta renalis  14  and vena renalis  15  are shown as well. A first external electrode  440  is connected via line  51  to a control unit  50  (not shown). A renal coil electrode  540  is positioned in the vena renalis  15  to allow a current flow between this electrode  540  and said external patch electrode  440 . The connection of the renal coil electrode  540  to the control unit  50  is effected via the catheter line  53  used to position the renal coil electrode  540 . The coil electrode could in other embodiments also positioned in the renal lymphatic system. 
     
       
         
           
               
             
               
                   
               
               
                 LIST OF REFERENCE SIGNS 
               
               
                   
               
             
            
               
                   
               
            
           
           
               
               
            
               
                 10 
                 heart (internal organ) 
               
               
                 11 
                 kidney (internal organ) 
               
               
                 12 
                 ureter 
               
               
                 13 
                 aorta or vena renalis 
               
               
                 14 
                 aorta renalis 
               
               
                 15 
                 vena renalis 
               
               
                 16 
                 renal calix 
               
               
                 17 
                 renal pyramid 
               
               
                 18 
                 renal pelvis 
               
               
                 20 
                 electrode assembly 
               
               
                 30 
                 ventricular coil electrode 
               
               
                 40 
                 coil electrode for coronary sinus 
               
               
                 50 
                 control circuit 
               
               
                 51 
                 single-conductor supply line 
               
               
                 52 
                 single-conductor supply line 
               
               
                 53 
                 renal catheter line 
               
               
                 55 
                 arrow indicating DC current flow 
               
               
                 60 
                 person 
               
               
                 70 
                 patch electrode surface 
               
               
                 72 
                 opening 
               
               
                 73 
                 diaphragm valve 
               
               
                 75 
                 electrode surface 
               
               
                 77 
                 water flow 
               
               
                 140  
                 external patch electrode 
               
               
                 141  
                 edge of the surface electrode 
               
               
                 152  
                 single-conductor supply line 
               
               
                 155  
                 arrow indicating DC current flow 
               
               
                 240  
                 first external patch electrode 
               
               
                 340  
                 second external patch electrode 
               
               
                 440  
                 first external patch electrode 
               
               
                 440′  
                 second external patch electrode 
               
               
                 540  
                 renal coil electrode