reference is made to fig1 a - 1e which schematically illustrate various stages of a cell division process . fig1 a illustrates a cell 10 at its normal geometry , which can be generally spherical ( as illustrated in the drawings ), ellipsoidal , cylindrical , “ pancake - like ” or any other cell geometry , as is known in the art . fig1 b - 1d illustrate cell 10 during different stages of its division process , which results in the formation of two new cells 18 and 20 , shown in fig1 e . as shown in fig1 b - 1d , the division process of cell 10 is characterized by a slowly growing cleft 12 which gradually separates cell 10 into two units , namely sub - cells 14 and 16 , which eventually evolve into new cells 18 and 20 ( fig1 e ). a shown specifically in fig1 d , the division process is characterized by a transient period during which the structure of cell 10 is basically that of the two sub - cells 14 and 16 interconnected by a narrow “ bridge ” 22 containing cell material ( cytoplasm surrounded by cell membrane ). reference is now made to fig2 a and 2b , which schematically illustrate non - dividing cell 10 being subjected to an electric field produced by applying an alternating electric potential , at a relatively low frequency and at a relatively high frequency , respectively . cell 10 includes intracellular organelles , e . g ., a nucleus 30 . alternating electric potential is applied across electrodes 28 and 32 that can be attached externally to a patient at a predetermined region , e . g ., in the vicinity of the tumor being treated . when cell 10 is under natural conditions , i . e ., part of a living tissue , it is disposed in a conductive environment ( hereinafter referred to as a “ volume conductor ”) consisting mostly of electrolytic inter - cellular liquid . when an electric potential is applied across electrodes 28 and 32 , some of the field lines of the resultant electric field ( or the current induced in the tissue in response to the electric field ) penetrate the cell 10 , while the rest of the field lines ( or induced current ) flow in the surrounding medium . the specific distribution of the electric field lines , which is substantially consistent with the direction of current flow in this instance , depends on the geometry and the electric properties of the system components , e . g ., the relative conductivities and dielectric constants of the system components , that can be frequency dependent . for low frequencies , e . g ., frequencies lower than 10 khz , the conductance properties of the components completely dominate the current flow and the field distribution , and the field distribution is generally as depicted in fig2 a . at higher frequencies , e . g ., at frequencies of between 10 khz and 1 mhz , the dielectric properties of the components becomes more significant and eventually dominate the field distribution , resulting in field distribution lines as depicted generally in fig2 b . for constant ( i . e ., dc ) electric fields or relatively low frequency alternating electric fields , for example , frequencies under 10 khz , the dielectric properties of the various components are not significant in determining and computing the field distribution . therefore , as a first approximation , with regard to the electric field distribution , the system can be reasonably represented by the relative impedances of its various components . using this approximation , the intercellular ( i . e ., extracellular ) fluid and the intracellular fluid each has a relatively low impedance , while the cell membrane 11 has a relatively high impedance . thus , under low frequency conditions , only a fraction of the electric field lines ( or currents induced by the electric field ) penetrate membrane 11 of the cell 10 . at relatively high frequencies ( e . g ., 10 khz - 1 mhz ), in contrast , the impedance of membrane 11 relative to the intercellular and intracellular fluids decreases , and thus , the fraction of currents penetrating the cells increases significantly . it should be noted that at very high frequencies , i . e ., above 1 mhz , the membrane capacitance can short the membrane resistance and , therefore , the total membrane resistance can become negligible . in any of the embodiments described above , the electric field lines ( or induced currents ) penetrate cell 10 from a portion of the membrane 11 closest to one of the electrodes generating the current , e . g ., closest to positive electrode 28 ( also referred to herein as “ source ”). the current flow pattern across cell 10 is generally uniform because , under the above approximation , the field induced inside the cell is substantially homogeneous . the currents exit cell 10 through a portion of membrane 11 closest to the opposite electrode , e . g ., negative electrode 32 ( also referred to herein as “ sink ”). the distinction between field lines and current flow can depend on a number of factors , for example , on the frequency of the applied electric potential and on whether electrodes 28 and 32 are electrically insulated . for insulated electrodes applying a dc or low frequency alternating voltage , there is practically no current flow along the lines of the electric field . at higher frequencies , the displacement currents are induced in the tissue due to charging and discharging of the electrode insulation and the cell membranes ( which act as capacitors to a certain extent ), and such currents follow the lines of the electric field . fields generated by non - insulated electrodes , in contrast , always generate some form of current flow , specifically , dc or low frequency alternating fields generate conductive current flow along the field lines , and high frequency alternating fields generate both conduction and displacement currents along the field lines . it should be appreciated , however , that movement of polarizable intracellular organelles according to the present invention ( as described below ) is not dependent on actual flow of current and , therefore , both insulated and non - insulated electrodes can be used efficiently . several advantages of insulated electrodes are that they have lower power consumption and cause less heating of the treated regions . according to one exemplary embodiment of the present invention , the electric fields that are used are alternating fields having frequencies that are in the range from about 50 khz to about 500 khz , and preferably from about 100 khz to about 300 khz . for ease of discussion , these type of electric fields are also referred to below as “ tc fields ”, which is an abbreviation of “ tumor curing electric fields ”, since these electric fields fall into an intermediate category ( between high and low frequency ranges ) that have bio - effective field properties while having no meaningful stimulatory and thermal effects . these frequencies are sufficiently low so that the system behavior is determined by the system &# 39 ; s ohmic ( conductive ) properties but sufficiently high enough not to have any stimulation effect on excitable tissues . such a system consists of two types of elements , namely , the intercellular , or extracellular fluid , or medium and the individual cells . the intercellular fluid is mostly an electrolyte with a specific resistance of about 40 - 100 ohm * cm . as mentioned above , the cells are characterized by three elements , namely ( 1 ) a thin , highly electric resistive membrane that coats the cell ; ( 2 ) internal cytoplasm that is mostly an electrolyte that contains numerous macromolecules and micro - organelles , including the nucleus ; and ( 3 ) membranes , similar in their electric properties to the cell membrane , cover the micro - organelles . when this type of system is subjected to the present tc fields ( e . g ., alternating electric fields in the frequency range of 100 khz - 300 khz ) most of the lines of the electric field and currents tend away from the cells because of the high resistive cell membrane and therefore the lines remain in the extracellular conductive medium . in the above recited frequency range , the actual fraction of electric field or currents that penetrates the cells is a strong function of the frequency . fig2 schematically depicts the resulting field distribution in the system . as illustrated , the lines of force , which also depict the lines of potential current flow across the cell volume mostly in parallel with the undistorted lines of force ( the main direction of the electric field ). in other words , the field inside the cells is mostly homogeneous . in practice , the fraction of the field or current that penetrates the cells is determined by the cell membrane impedance value relative to that of the extracellular fluid . since the equivalent electric circuit of the cell membrane is that of a resistor and capacitor in parallel , the impedance is a function of the frequency . the higher the frequency , the lower the impedance , the larger the fraction of penetrating current and the smaller the field distortion . as previously mentioned , when cells are subjected to relatively weak electric fields and currents that alternate at high frequencies , such as the present tc fields having a frequency in the range of 50 khz - 500 khz , they have no effect on the non - dividing cells . while the present tc fields have no detectable effect on such systems , the situation becomes different in the presence of dividing cells . reference is now made to fig3 a - 3c which schematically illustrate the electric current flow pattern in cell 10 during its division process , under the influence of alternating fields ( tc fields ) in the frequency range from about 100 khz to about 300 khz in accordance with one exemplary embodiment . the field lines or induced currents penetrate cell 10 through a part of the membrane of sub - cell 16 closer to electrode 28 . however , they do not exit through the cytoplasm bridge 22 that connects sub - cell 16 with the newly formed yet still attached sub - cell 14 , or through a part of the membrane in the vicinity of the bridge 22 . instead , the electric field or current flow lines — that are relatively widely separated in sub - cell 16 — converge as they approach bridge 22 ( also referred to as “ neck ” 22 ) and , thus , the current / field line density within neck 22 is increased dramatically . a “ mirror image ” process takes place in sub - cell 14 , whereby the converging field lines in bridge 22 diverge as they approach the exit region of sub - cell 14 . it should be appreciated by persons skilled in the art that homogeneous electric fields do not exert a force on electrically neutral objects , i . e ., objects having substantially zero net charge , although such objects can become polarized . however , under a non - uniform , converging electric field , as shown in fig3 a - 3c , electric forces are exerted on polarized objects , moving them in the direction of the higher density electric field lines . it will be appreciated that the concentrated electric field that is present in the neck or bridge area in itself exerts strong forces on charges and natural dipoles and can disrupt structures that are associated therewith . one will understand that similar net forces act on charges in an alternating field , again in the direction of the field of higher intensity . in the configuration of fig3 a and 3b , the direction of movement of polarized and charged objects is towards the higher density electric field lines , i . e ., towards the cytoplasm bridge 22 between sub - cells 14 and 16 . it is known in the art that all intracellular organelles , for example , nuclei 24 and 26 of sub - cells 14 and 16 , respectively , are polarizable and , thus , such intracellular organelles are electrically forced in the direction of the bridge 22 . since the movement is always from lower density currents to the higher density currents , regardless of the field polarity , the forces applied by the alternating electric field to organelles , such as nuclei 24 and 26 , are always in the direction of bridge 22 . a comprehensive description of such forces and the resulting movement of macromolecules of intracellular organelles , a phenomenon referred to as “ dielectrophoresis ” is described extensively in literature , e . g ., in c . l . asbury & amp ; g . van den engh , biophys . j . 74 , 1024 - 1030 , 1998 , the disclosure of which is hereby incorporated by reference in its entirety . the movement of the organelles 24 and 26 towards the bridge 22 disrupts the structure of the dividing cell , change the concentration of the various cell constituents and , eventually , the pressure of the converging organelles on bridge membrane 22 results in the breakage of cell membrane 11 at the vicinity of the bridge 22 , as shown schematically in fig3 c . the ability to break membrane 11 at bridge 22 and to otherwise disrupt the cell structure and organization can be enhanced by applying a pulsating ac electric field , rather than a steady ac field . when a pulsating field is applied , the forces acting on organelles 24 and 26 have a “ hammering ” effect , whereby pulsed forces beat on the intracellular organelles towards the neck 22 from both sub - cells 14 and 16 , thereby increasing the probability of breaking cell membrane 11 in the vicinity of neck 22 . a very important element , which is very susceptible to the special fields that develop within the dividing cells is the microtubule spindle that plays a major role in the division process . in fig4 , a dividing cell 10 is illustrated , at an earlier stage as compared to fig3 a and 3b , under the influence of external tc fields ( e . g ., alternating fields in the frequency range of about 100 khz to about 300 khz ), generally indicated as lines 100 , with a corresponding spindle mechanism generally indicated at 120 . the lines 120 are microtubules that are known to have a very strong dipole moment . this strong polarization makes the tubules susceptible to electric fields . their positive charges are located at the two centrioles while two sets of negative poles are at the center of the dividing cell and the other pair is at the points of attachment of the microtubules to the cell membrane , generally indicated at 130 . this structure forms sets of double dipoles and therefore they are susceptible to fields of different directions . it will be understood that the effect of the tc fields on the dipoles does not depend on the formation of the bridge ( neck ) and thus , the dipoles are influenced by the tc fields prior to the formation of the bridge ( neck ). since the present apparatus ( as will be described in greater detail below ) utilizes insulated electrodes , the above - mentioned negative effects obtained when conductive electrodes are used , i . e ., ion concentration changes in the cells and the formation of harmful agents by electrolysis , do not occur when the present apparatus is used . this is because , in general , no actual transfer of charges takes place between the electrodes and the medium and there is no charge flow in the medium where the currents are capacitive , i . e ., are expressed only as rotation of charges , etc . turning now to fig5 , the tc fields described above that have been found to advantageously destroy tumor cells are generated by an electronic apparatus 200 . fig5 is a simple schematic diagram of the electronic apparatus 200 illustrating the major components thereof the electronic apparatus 200 generates the desired electric signals ( tc signals ) in the shape of waveforms or trains of pulses . the apparatus 200 includes a generator 210 and a pair of conductive leads 220 that are attached at one end thereof to the generator 210 . the opposite ends of the leads 220 are connected to insulated conductors 230 that are activated by the electric signals ( e . g ., waveforms ). the insulated conductors 230 are also referred to hereinafter as isolects 230 . optionally and according to another exemplary embodiment , the apparatus 200 includes a temperature sensor 240 and a control box 250 which are both added to control the amplitude of the electric field generated so as not to generate excessive heating in the area that is treated . the generator 210 generates an alternating voltage waveform at frequencies in the range from about 50 khz to about 500 khz ( preferably from about 100 khz to about 300 khz ) ( i . e ., the tc fields ). the required voltages are such that the electric field intensity in the tissue to be treated is in the range of about 0 . 1 v / cm to about 10 v / cm . to achieve this field , the actual potential difference between the two conductors in the isolects 230 is determined by the relative impedances of the system components , as described below . when the control box 250 is included , it controls the output of the generator 210 so that it will remain constant at the value preset by the user or the control box 250 sets the output at the maximal value that does not cause excessive heating , or the control box 250 issues a warning or the like when the temperature ( sensed by temperature sensor 240 ) exceeds a preset limit . the leads 220 are standard isolated conductors with a flexible metal shield , preferably grounded so that it prevents the spread of the electric field generated by the leads 220 . the isolects 230 have specific shapes and positioning so as to generate an electric field of the desired configuration , direction and intensity at the target volume and only there so as to focus the treatment . the specifications of the apparatus 200 as a whole and its individual components are largely influenced by the fact that at the frequency of the present tc fields ( 50 khz - 500 khz ), living systems behave according to their “ ohmic ”, rather than their dielectric properties . the only elements in the apparatus 200 that behave differently are the insulators of the isolects 230 ( see fig7 - 9 ). the isolects 200 consist of a conductor in contact with a dielectric that is in contact with the conductive tissue thus forming a capacitor . the details of the construction of the isolects 230 is based on their electric behavior that can be understood from their simplified electric circuit when in contact with tissue as generally illustrated in fig6 . in the illustrated arrangement , the potential drop or the electric field distribution between the different components is determined by their relative electric impedance , i . e ., the fraction of the field on each component is given by the value of its impedance divided by the total circuit impedance . for example , the potential drop on element ? v a = a /( a + b + c + d + e ). thus , for dc or low frequency ac , practically all the potential drop is on the capacitor ( that acts as an insulator ). for relatively very high frequencies , the capacitor practically is a short and therefore , practically all the field is distributed in the tissues . at the frequencies of the present tc fields ( e . g ., 50 khz to 500 khz ), which are intermediate frequencies , the impedance of the capacitance of the capacitors is dominant and determines the field distribution . therefore , in order to increase the effective voltage drop across the tissues ( field intensity ), the impedance of the capacitors is to be decreased ( i . e ., increase their capacitance ). this can be achieved by increasing the effective area of the “ plates ” of the capacitor , decrease the thickness of the dielectric or use a dielectric with high dielectric constant . in order to optimize the field distribution , the isolects 230 are configured differently depending upon the application in which the isolects 230 are to be used . there are two principle modes for applying the present electric fields ( tc fields ). first , the tc fields can be applied by external isolects and second , the tc fields can be applied by internal isolects . electric fields ( tc fields ) that are applied by external isolects can be of a local type or widely distributed type . the first type includes , for example , the treatment of skin tumors and treatment of lesions close to the skin surface . fig7 illustrates an exemplary embodiment where the isolects 230 are incorporated in a skin patch 300 . the skin patch 300 can be a self - adhesive flexible patch with one or more pairs of isolects 230 . the patch 300 includes internal insulation 310 ( formed of a dielectric material ) and the external insulation 260 and is applied to skin surface 301 that contains a tumor 303 either on the skin surface 301 or slightly below the skin surface 301 . tissue is generally indicated at 305 . to prevent the potential drop across the internal insulation 310 to dominate the system , the internal insulation 310 must have a relatively high capacity . this can be achieved by a large surface area ; however , this may not be desired as it will result in the spread of the field over a large area ( e . g ., an area larger than required to treat the tumor ). alternatively , the internal insulation 310 can be made very thin and / or the internal insulation 310 can be of a high dielectric constant . as the skin resistance between the electrodes ( labeled as a and e in fig6 ) is normally significantly higher than that of the tissue ( labeled as c in fig6 ) underneath it ( 1 - 10 ko vs . 0 . 1 - 1 ko ), most of the potential drop beyond the isolects occurs there . to accommodate for these impedances ( z ), the characteristics of the internal insulation 310 ( labeled as b and d in fig6 ) should be such that they have impedance preferably under 100 ko at the frequencies of the present tc fields ( e . g ., 50 khz to 500 khz ). for example , if it is desired for the impedance to be about 10k ohms or less , such that over 1 % of the applied voltage falls on the tissues , for isolects with a surface area of 10 mm 2 , at frequencies of 200 khz , the capacity should be on the order of 10 − 10 f , which means that using standard insulations with a dielectric constant of 2 - 3 , the thickness of the insulating layer 310 should be about 50 - 100 microns . an internal field 10 times stronger would be obtained with insulators with a dielectric constant of about 20 - 50 . since the thin insulating layer can be very vulnerable , etc ., the insulation can be replaced by very high dielectric constant insulating materials , such as titanium dioxide ( e . g ., rutil ), the dielectric constant can reach values of about 200 . there a number of different materials that are suitable for use in the intended application and have high dielectric constants . for example , some materials include : lithium nibate ( linbo 3 ), which is a ferroelectric crystal and has a number of applications in optical , pyroelectric and piezoelectric devices ; yttrium iron garnet ( yig ) is a ferromagnetic crystal and magneto - optical devices , e . g ., optical isolator can be realized from this material ; barium titanate ( batio 3 ) is a ferromagnetic crystal with a large electro - optic effect ; potassium tantalate ( ktao 3 ) which is a dielectric crystal ( ferroelectric at low temperature ) and has very low microwave loss and tunability of dielectric constant at low temperature ; and lithium tantalate ( litao 3 ) which is a ferroelectric crystal with similar properties as lithium niobate and has utility in electro - optical , pyroelectric and piezoelectric devices . it will be understood that the aforementioned exemplary materials can be used in combination with the present device where it is desired to use a material having a high dielectric constant . one must also consider another factor that effects the effective capacity of the isolects 230 , namely the presence of air between the isolects 230 and the skin . such presence , which is not easy to prevent , introduces a layer of an insulator with a dielectric constant of 1 . 0 , a factor that significantly lowers the effective capacity of the isolects 230 and neutralizes the advantages of the titanium dioxide ( rutil ), etc . to overcome this problem , the isolects 230 can be shaped so as to conform with the body structure and / or ( 2 ) an intervening filler 270 ( as illustrated in fig1 c ), such as a gel , that has high conductance and a high effective dielectric constant , can be added to the structure . the shaping can be pre - structured ( see fig1 a ) or the system can be made sufficiently flexible so that shaping of the isolects 230 is readily achievable . the gel can be contained in place by having an elevated rim as depicted in fig1 c . the gel can be made of hydrogels , gelatins , agar , etc ., and can have salts dissolved in it to increase its conductivity . fig1 a - 10c illustrate various exemplary configurations for the isolects 230 . the exact thickness of the gel is not important so long as it is of sufficient thickness that the gel layer does not dry out during the treatment . in one exemplary embodiment , the thickness of the gel is about 0 . 5 mm to about 2 mm . in order to achieve the desirable features of the isolects 230 , the dielectric coating of each should be very thin , for example from between 1 - 50 microns . since the coating is so thin , the isolects 230 can easily be damaged mechanically . this problem can be overcome by adding a protective feature to the isolect &# 39 ; s structure so as to provide desired protection from such damage . for example , the isolect 230 can be coated , for example , with a relatively loose net 340 that prevents access to the surface but has only a minor effect on the effective surface area of the isolect 230 ( i . e ., the capacity of the isolects 230 ( cross section presented in fig1 b ). the loose net 340 does not effect the capacity and ensures good contact with the skin , etc . the loose net 340 can be formed of a number of different materials ; however , in one exemplary embodiment , the net 340 is formed of nylon , polyester , cotton , etc . alternatively , a very thin conductive coating 350 can be applied to the dielectric portion ( insulating layer ) of the isolect 230 . one exemplary conductive coating is formed of a metal and more particularly of gold . the thickness of the coating 350 depends upon the particular application and also on the type of material used to form the coating 350 ; however , when gold is used , the coating has a thickness from about 0 . 1 micron to about 0 . 1 mm . furthermore , the rim illustrated in fig1 can also provide some mechanical protection . however , the capacity is not the only factor to be considered . the following two factors also influence how the isolects 230 are constructed . the dielectric strength of the internal insulating layer 310 and the dielectric losses that occur when it is subjected to the tc field , i . e ., the amount of heat generated . the dielectric strength of the internal insulation 310 determines at what field intensity the insulation will be “ shorted ” and cease to act as an intact insulation . typically , insulators , such as plastics , have dielectric strength values of about 100 v per micron or more . as a high dielectric constant reduces the field within the internal insulator 310 , a combination of a high dielectric constant and a high dielectric strength gives a significant advantage . this can be achieved by using a single material that has the desired properties or it can be achieved by a double layer with the correct parameters and thickness . in addition , to further decreasing the possibility that the insulating layer 310 will fail , all sharp edges of the insulating layer 310 should be eliminated as by rounding the corners , etc ., as illustrated in fig1 d using conventional techniques . fig8 and 9 illustrate a second type of treatment using the isolects 230 , namely electric field generation by internal isolects 230 . a body to which the isolects 230 are implanted is generally indicated at 311 and includes a skin surface 313 and a tumor 315 . in this embodiment , the isolects 230 can have the shape of plates , wires or other shapes that can be inserted subcutaneously or a deeper location within the body 311 so as to generate an appropriate field at the target area ( tumor 315 ). it will also be appreciated that the mode of isolects application is not restricted to the above descriptions . in the case of tumors in internal organs , for example , liver , lung , etc ., the distance between each member of the pair of isolects 230 can be large . the pairs can even by positioned opposite sides of a torso 410 , as illustrated in fig1 . the arrangement of the isolects 230 in fig1 is particularly useful for treating a tumor 415 associated with lung cancer or gastrointestinal tumors . in this embodiment , the electric fields ( tc fields ) spread in a wide fraction of the body . in order to avoid overheating of the treated tissues , a selection of materials and field parameters is needed . the isolects insulating material should have minimal dielectric losses at the frequency ranges to be used during the treatment process . this factor can be taken into consideration when choosing the particular frequencies for the treatment . the direct heating of the tissues will most likely be dominated by the heating due to current flow ( given by the i * r product ). in addition , the isolect ( insulated electrode ) 230 and its surroundings should be made of materials that facilitate heat losses and its general structure should also facilitate head losses , i . e ., minimal structures that block heat dissipation to the surroundings ( air ) as well as high heat conductivity . the effectiveness of the treatment can be enhanced by an arrangement of isolects 230 that focuses the field at the desired target while leaving other sensitive areas in low field density ( i . e ., protected areas ). the proper placement of the isolects 230 over the body can be maintained using any number of different techniques , including using a suitable piece of clothing that keeps the isolects at the appropriate positions . fig1 illustrates such an arrangement in which an area labeled as “ p ” represents a protected area . the lines of field force do not penetrate this protected area and the field there is much smaller than near the isolects 230 where target areas can be located and treated well . in contrast , the field intensity near the four poles is very high . the following example serves to illustrate an exemplary application of the present apparatus and application of tc fields ; however , this example is not limiting and does not limit the scope of the present invention in any way . to demonstrate the effectiveness of electric fields having the above described properties ( e . g ., frequencies between 50 khz and 500 khz ) in destroying tumor cells , the electric fields were applied to treat mice with malignant melanoma tumors . two pairs of isolects 230 were positioned over a corresponding pair of malignant melanomas . only one pair was connected to the generator 210 and 200 khz alternating electric fields ( tc fields ) were applied to the tumor for a period of 6 days . one melanoma tumor was not treated so as to permit a comparison between the treated tumor and the non - treated tumor . after treatment for 6 days , the pigmented melanoma tumor remained clearly visible in the non - treated side of the mouse , while , in contrast , no tumor is seen on the treated side of the mouse . the only areas that were visible discernable on the skin were the marks that represented the points of insertion of the isolects 230 . the fact that the tumor was eliminated at the treated side was further demonstrated by cutting and inversing the skin so that its inside face was exposed . such a procedure indicated that the tumor has been substantially , if not completely , eliminated on the treated side of the mouse . the success of the treatment was also further verified by pathhistological examination . the present inventor has thus uncovered that electric fields having particular properties can be used to destroy dividing cells or tumors when the electric fields are applied to using an electronic device . more specifically , these electric fields fall into a special intermediate category , namely bio - effective fields that have no meaningful stimulatory and no thermal effects , and therefore overcome the disadvantages that were associated with the application of conventional electric fields to a body . it will also be appreciated that the present apparatus can further include a device for rotating the tc field relative to the living tissue . for example and according to one embodiment , the alternating electric potential applies to the tissue being treated is rotated relative to the tissue using conventional devices , such as a mechanical device that upon activation , rotates various components of the present system . moreover and according to yet another embodiment , the tc fields are applied to different pairs of the insulated electrodes 230 in a consecutive manner . in other words , the generator 210 and the control system thereof can be arranged so that signals are sent at periodic intervals to select pairs of insulated electrodes 230 , thereby causing the generation of the tc fields of different directions by these insulated electrodes 230 . because the signals are sent at select times from the generator to the insulated electrodes 230 , the tc fields of changing directions are generated consecutively by different insulated electrodes 230 . this arrangement has a number of advantages and is provided in view of the fact that the tc fields have maximal effect when they are parallel to the axis of cell division . since the orientation of cell division is in most cases random , only a fraction of the dividing cells are affected by any given field . thus , using fields of two or more orientations increases the effectiveness since it increases the chances that more dividing cells are affected by a given tc field . turning now to fig1 in which an article of clothing 500 according to one exemplary embodiment is illustrated . more specifically , the article of clothing 500 is in the form of a hat or cap or other type of clothing designed for placement on a head of a person . for purposes of illustration , a head 502 is shown with the hat 500 being placed thereon and against a skin surface 504 of the head 502 . an intra - cranial tumor or the like 510 is shown as being formed within the head 502 underneath the skin surface 504 thereof the hat 500 is therefore intended for placement on the head 502 of a person who has a tumor 510 or the like . unlike the various embodiments illustrated in fig1 - 13 where the insulated electrodes 230 are arranged in a more or less planar arrangement since they are placed either on a skin surface or embedded within the body underneath it , the insulated electrodes 230 in this embodiment are specifically contoured and arranged for a specific application . the treatment of intra - cranial tumors or other lesions or the like typically requires a treatment that is of a relatively long duration , e . g ., days to weeks , and therefore , it is desirable to provide as much comfort as possible to the patient . the hat 500 is specifically designed to provide comfort during the lengthy treatment process while not jeopardizing the effectiveness of the treatment . according to one exemplary embodiment , the hat 500 includes a predetermined number of insulated electrodes 230 that are preferably positioned so as to produce the optimal tc fields at the location of the tumor 510 . the lines of force of the tc field are generally indicated at 520 . as can be seen in fig1 , the tumor 500 is positioned within these lines of force 520 . as will be described in greater detail hereinafter , the insulated electrodes 230 are positioned within the hat 500 such that a portion or surface thereof is free to contact the skin surface 504 of the head 502 . in other words , when the patient wears the hat 500 , the insulated electrodes 230 are placed in contact with the skin surface 504 of the head 502 in positions that are selected so that the tc fields generated thereby are focused at the tumor 510 while leaving surrounding areas in low density . typically , hair on the head 502 is shaved in selected areas to permit better contact between the insulated electrodes 230 and the skin surface 504 ; however , this is not critical . the hat 500 preferably includes a mechanism 530 that applies or force to the insulated electrodes 230 so that they are pressed against the skin surface 502 . for example , the mechanism 530 can be of a biasing type that applies a biasing force to the insulated electrodes 230 to cause the insulated electrodes 230 to be directed outwardly away from the hat 500 . thus , when the patient places the hat 500 on his / her head 502 , the insulated electrodes 230 are pressed against the skin surface 504 by the mechanism 530 . the mechanism 530 can slightly recoil to provide a comfortable fit between the insulated electrodes 230 and the head 502 . in one exemplary embodiment , the mechanism 530 is a spring based device that is disposed within the hat 500 and has one section that is coupled to and applies a force against the insulated electrodes 230 . as with the prior embodiments , the insulated electrodes 230 are coupled to the generator 210 by means of conductors 220 . the generator 210 can be either disposed within the hat 500 itself so as to provide a compact , self - sufficient , independent system or the generator 210 can be disposed external to the hat 500 with the conductors 220 exiting the hat 500 through openings or the like and then running to the generator 210 . when the generator 210 is disposed external to the hat 500 , it will be appreciated that the generator 210 can be located in any number of different locations , some of which are in close proximity to the hat 500 itself , while others can be further away from the hat 500 . for example , the generator 210 can be disposed within a carrying bag or the like ( e . g ., a bag that extends around the patient &# 39 ; s waist ) which is worn by the patient or it can be strapped to an extremity or around the torso of the patient . the generator 210 can also be disposed in a protective case that is secured to or carried by another article of clothing that is worn by the patient . for example , the protective case can be inserted into a pocket of a sweater , etc . fig1 illustrates an embodiment where the generator 210 is incorporated directly into the hat 500 . turning now to fig1 and 16 , in one exemplary embodiment , a number of insulated electrodes 230 along with the mechanism 530 are preferably formed as an independent unit , generally indicated at 540 , that can be inserted into the hat 500 and electrically connected to the generator ( not shown ) via the conductors ( not shown ). by providing these members in the form of an independent unit , the patient can easily insert and / or remove the units 540 from the hat 500 when they may need cleaning , servicing and / or replacement . in this embodiment , the hat 500 is constructed to include select areas 550 that are formed in the hat 500 to receive and hold the units 540 . for example and as illustrated in fig1 , each area 550 is in the form of an opening ( pore ) that is formed within the hat 500 . the unit 540 has a body 542 and includes the mechanism 530 and one or more insulated electrodes 230 . the mechanism 530 is arranged within the unit 540 so that a portion thereof ( e . g ., one end thereof ) is in contact with a face of each insulated electrode 230 such that the mechanism 530 applies a biasing force against the face of the insulated electrode 230 . once the unit 540 is received within the opening 550 , it can be securely retained therein using any number of conventional techniques , including the use of an adhesive material or by using mechanical means . for example , the hat 500 can include pivotable clip members that pivot between an open position in which the opening 550 is free and a closed position in which the pivotable clip members engage portions ( e . g ., peripheral edges ) of the insulated electrodes to retain and hold the insulated electrodes 230 in place . to remove the insulated electrodes 230 , the pivotable clip members are moved to the open position . in the embodiment illustrated in fig1 , the insulated electrodes 230 are retained within the openings 550 by an adhesive element 560 which in one embodiment is a two sided self - adhesive rim member that extends around the periphery of the insulated electrode 230 . in other words , a protective cover of one side of the adhesive rim 560 is removed and it is applied around the periphery of the exposed face of the insulated electrode 230 , thereby securely attaching the adhesive rim 560 to the hat 500 and then the other side of the adhesive rim 560 is removed for application to the skin surface 504 in desired locations for positioning and securing the insulated electrode 230 to the head 502 with the tumor being positioned relative thereto for optimization of the tc fields . since one side of the adhesive rim 560 is in contact with and secured to the skin surface 540 , this is why it is desirable for the head 502 to be shaved so that the adhesive rim 560 can be placed fleshly against the skin surface 540 . the adhesive rim 560 is designed to securely attach the unit 540 within the opening 550 in a manner that permits the unit 540 to be easily removed from the hat 500 when necessary and then replaced with another unit 540 or with the same unit 540 . as previously mentioned , the unit 540 includes the biasing mechanism 530 for pressing the insulated electrode 230 against the skin surface 504 when the hat 500 is worn . the unit 540 can be constructed so that the side opposite the insulated electrode 230 is a support surface formed of a rigid material , such as plastic , so that the biasing mechanism 530 ( e . g ., a spring ) can be compressed therewith under the application of force and when the spring 530 is in a relaxed state , the spring 530 remains in contact with the support surface and the applies a biasing force at its other end against the insulated electrode 230 . the biasing mechanism 530 ( e . g ., spring ) preferably has a contour corresponding to the skin surface 504 so that the insulated electrode 230 has a force applied thereto to permit the insulated electrode 230 to have a contour complementary to the skin surface 504 , thereby permitting the two to seat fleshly against one another . while the mechanism 530 can be a spring , there are a number of other embodiments that can be used instead of a spring . for example , the mechanism 530 can be in the form of an elastic material , such as a foam rubber , a foam plastic , or a layer containing air bubbles , etc . the unit 540 has an electric connector 570 that can be hooked up to a corresponding electric connector , such as a conductor 220 , that is disposed within the hat 500 . the conductor 220 connects at one end to the unit 540 and at the other end is connected to the generator 210 . the generator 210 can be incorporated directly into the hat 500 or the generator 210 can be positioned separately ( remotely ) on the patient or on a bedside support , etc . as previously discussed , a coupling agent , such as a conductive gel , is preferably used to ensure that an effective conductive environment is provided between the insulated electrode 230 and the skin surface 504 . suitable gel materials have been disclosed hereinbefore in the discussion of earlier embodiments . the coupling agent is disposed on the insulated electrode 230 and preferably , a uniform layer of the agent is provided along the surface of the electrode 230 . one of the reasons that the units 540 need replacement at periodic times is that the coupling agent needs to be replaced and / or replenished . in other words , after a predetermined time period or after a number of uses , the patient removes the units 540 so that the coupling agent can be applied again to the electrode 230 . fig1 and 18 illustrate another article of clothing which has the insulated electrodes 230 incorporated as part thereof more specifically , a bra or the like 700 is illustrated and includes a body that is formed of a traditional bra material , generally indicated at 705 , to provide shape , support and comfort to the wearer . the bra 700 also includes a fabric support layer 710 on one side thereof the support layer 710 is preferably formed of a suitable fabric material that is constructed to provide necessary and desired support to the bra 700 . similar to the other embodiments , the bra 700 includes one or more insulated electrodes 230 disposed within the bra material 705 . the one or more insulated electrodes are disposed along an inner surface of the bra 700 opposite the support 710 and are intended to be placed proximate to a tumor or the like that is located within one breast or in the immediately surrounding area . as with the previous embodiment , the insulated electrodes 230 in this embodiment are specifically constructed and configured for application to a breast or the immediate area . thus , the insulated electrodes 230 used in this application do not have a planar surface construction but rather have an arcuate shape that is complementary to the general curvature found in a typical breast . a lining 720 is disposed across the insulated electrodes 230 so as to assist in retaining the insulated electrodes in their desired locations along the inner surface for placement against the breast itself . the lining 720 can be formed of any number of thin materials that are comfortable to wear against one &# 39 ; s skin and in one exemplary embodiment , the lining 720 is formed of a fabric material . the bra 700 also preferably includes a biasing mechanism 800 as in some of the earlier embodiments . the biasing mechanism 800 is disposed within the bra material 705 and extends from the support 710 to the insulated electrode 230 and applies a biasing force to the insulated electrode 230 so that the electrode 230 is pressed against the breast . this ensures that the insulated electrode 230 remains in contact with the skin surface as opposed to lifting away from the skin surface , thereby creating a gap that results in a less effective treatment since the gap diminishes the efficiency of the tc fields . the biasing mechanism 800 can be in the form of a spring arrangement or it can be an elastic material that applies the desired biasing force to the insulated electrodes 230 so as to press the insulated electrodes 230 into the breast . in the relaxed position , the biasing mechanism 800 applies a force against the insulated electrodes 230 and when the patient places the bra 700 on their body , the insulated electrodes 230 are placed against the breast which itself applies a force that counters the biasing force , thereby resulting in the insulated electrodes 230 being pressed against the patient &# 39 ; s breast . in the exemplary embodiment that is illustrated , the biasing mechanism 800 is in the form of springs that are disposed within the bra material 705 . a conductive gel 810 can be provided on the insulated electrode 230 between the electrode and the lining 720 . the conductive gel layer 810 is formed of materials that have been previously described herein for performing the functions described above . an electric connector 820 is provided as part of the insulated electrode 230 and electrically connects to the conductor 220 at one end thereof , with the other end of the conductor 220 being electrically connected to the generator 210 . in this embodiment , the conductor 220 runs within the bra material 705 to a location where an opening is formed in the bra 700 . the conductor 220 extends through this opening and is routed to the generator 210 , which in this embodiment is disposed in a location remote from the bra 700 . it will also be appreciated that the generator 210 can be disposed within the bra 700 itself in another embodiment . for example , the bra 700 can have a compartment formed therein which is configured to receive and hold the generator 210 in place as the patient wears the bra 700 . in this arrangement , the compartment can be covered with a releasable strap that can open and close to permit the generator 210 to be inserted therein or removed therefrom . the strap can be formed of the same material that is used to construct the bra 700 or it can be formed of some other type of material . the strap can be releasably attached to the surrounding bra body by fastening means , such as a hook and loop material , thereby permitting the patient to easily open the compartment by separating the hook and loop elements to gain access to the compartment for either inserting or removing the generator 210 . the generator 210 also has a connector 211 for electrical connection to the conductor 220 and this permits the generator 210 to be electrically connected to the insulated electrodes 230 . as with the other embodiments , the insulated electrodes 230 are arranged in the bra 700 to focus the electric field ( tc fields ) on the desired target ( e . g ., a tumor ). it will be appreciated that the location of the insulated electrodes 230 within the bra 700 will vary depending upon the location of the tumor . in other words , after the tumor has been located , the physician will then devise an arrangement of insulated electrodes 230 and the bra 700 is constructed in view of this arrangement so as to optimize the effects of the tc fields on the target area ( tumor ). the number and position of the insulated electrodes 230 will therefore depend upon the precise location of the tumor or other target area that is being treated . because the location of the insulated electrodes 230 on the bra 700 can vary depending upon the precise application , the exact size and shape of the insulated electrodes 230 can likewise vary . for example , if the insulated electrodes 230 are placed on the bottom section of the bra 700 as opposed to a more central location , the insulated electrodes 230 will have different shapes since the shape of the breast ( as well as the bra ) differs in these areas . fig1 illustrates yet another embodiment in which the insulated electrodes 230 are in the form of internal electrodes that are incorporated into in the form of a probe or catheter 600 that is configured to enter the body through a natural pathway , such as the urethra , vagina , etc . in this embodiment , the insulated electrodes 230 are disposed on an outer surface of the probe 600 and along a length thereof the conductors 220 are electrically connected to the electrodes 230 and run within the body of the probe 600 to the generator 210 which can be disposed within the probe body or the generator 210 can be disposed independent of the probe 600 in a remote location , such as on the patient or at some other location close to the patient . alternatively , the probe 600 can be configured to penetrate the skin surface or other tissue to reach an internal target that lies within the body . for example , the probe 600 can penetrate the skin surface and then be positioned adjacent to or proximate to a tumor that is located within the body . in these embodiments , the probe 600 is inserted through the natural pathway and then is positioned in a desired location so that the insulated electrodes 230 are disposed near the target area ( i . e ., the tumor ). the generator 210 is then activated to cause the insulated electrodes 230 to generate the tc fields which are applied to the tumor for a predetermined length of time . it will be appreciated that the illustrated probe 600 is merely exemplary in nature and that the probe 600 can have other shapes and configurations so long as they can perform the intended function . preferably , the conductors ( e . g ., wires ) leading from the insulated electrodes 230 to the generator 210 are twisted or shielded so as not to generate a field along the shaft . fig2 illustrates yet another embodiment in which a high standing collar member 900 ( or necklace type structure ) can be used to treat thyroid , parathyroid , laryngeal lesions , etc . fig2 illustrates the collar member 900 in an unwrapped , substantially flat condition . in this embodiment , the insulated electrodes 230 are incorporated into a body 910 of the collar member 900 and are configured for placement against a neck area of the wearer . the insulated electrodes 230 are coupled to the generator 210 according to any of the manner described hereinbefore and it will be appreciated that the generator 210 can be disposed within the body 910 or it can be disposed in a location external to the body 910 . the collar body 910 can be formed of any number of materials that are traditionally used to form collars 900 that are disposed around a person &# 39 ; s neck . as such , the collar 900 preferably includes a means 920 for adjusting the collar 900 relative to the neck . for example , complementary fasteners ( hook and loop fasteners , buttons , etc .) can be disposed on ends of the collar 900 to permit adjustment of the collar diameter . thus , the construction of the present devices are particularly well suited for applications where the devices are incorporated into articles of clothing to permit the patient to easily wear a traditional article of clothing while at the same time the patient undergoes treatment . in other words , an extra level of comfort can be provided to the patient and the effectiveness of the treatment can be increased by incorporating some or all of the device components into the article of clothing . the precise article of clothing that the components are incorporated into will obviously vary depending upon the target area of the living tissue where tumor , lesion or the like exists . for example , if the target area is in the testicle area of a male patient , then an article of clothing in the form of a sock - like structure or wrap can be provided and is configured to be worn around the testicle area of the patient in such a manner that the insulated electrodes thereof are positioned relative to the tumor such that the tc fields are directed at the target tissue . the precise nature or form of the article of clothing can vary greatly since the device components can be incorporated into most types of articles of clothing and therefore , can be used to treat any number of different areas of the patient &# 39 ; s body where a condition may be present . while the invention has been particularly shown and described with reference to preferred embodiments thereof , it will be understood by those skilled in the art that various changes in form and details can be made without departing from the spirit and scope of the invention .
an article of clothing is pro - vided for selectively destroying dividing cells in living tissue formed of dividing cells and non - dividing cells . the dividing cells contain polarizable intracellular members and during late anaphase or telophase , the dividing cells are connected to one another by a cleavage furrow . the article of clothing includes insulated electrodes to be coupled to a generator for subjecting the living tissue to electric field conditions sufficient to cause movement of the polarizable intracellular members toward the cleavage furrow in response to a non - homogeneous electric field being induced in the dividing cells . the non - homogeneous electric field produces an increased density electric field in the region of the cleavage furrow . the movement of the polarizable intracellular intracellular members towards the cleavage furrow causes the breakdown thereof which adversely impacts the multiplication of the dividing cells .