fig1 and 2 show , each in the form of an equivalent circuit diagram with associated calculation bases , illustrations to explain the principle according to the invention in two embodiments . r 1 and l 1 designate an ohmic resistor and an inductor of a functional conductor , and l and c designate the inductance and capacitance , respectively , and rl and rc designate the corresponding loss resistances of an lc resonant circuit , which is used as the magnetic flux generation means to build up a magnetic flux , which can be coupled into the functional conductor to reduce the current flux built up therein by an external field . the lc resonant circuit is adapted on the foundation of the equations disclosed in the figures to the field frequency ( or a frequency band ) to be suppressed in the implant , in order to maximize the absolute value of the magnetic flux ( counter flux ). fig3 shows the results of a calculation ( simulation ) of the frequency - dependent impedance increase , which the inductive section of the functional conductor causes solely because of the inductive coupling with the magnetic flux generation means ( the “ magnetic flux barrier ”). the calculation parameters are as follows : the desired capacitance value c is calculated therefrom according to fig1 or fig2 . fig4 a schematically shows the design construction of the interior of an electrode line 1 , which comprises a coiled functional conductor 2 , which has an inductance l 1 in one section and in which a further conductor 3 having an inductance l is wound corradially , at equal diameter and equal pitch , with which a capacitance c is associated . fig4 b shows that the capacitance c can be implemented by a capacitor 4 enclosing the electrode coil 2 and / or 3 , which is constructed from two concentric metal cylinders 4 a , 4 b having a dielectric material 4 c situated between them . in order to achieve the capacitance in the pf range , which is required in the event of typical interfering fields , dielectric materials having a relative dielectric constant ( dk )& gt ; 8 may be used with respect to realistic dimensions of the magnetic flux generation section . fig5 shows , as a further embodiment , the electrode coil of a further electrode line 5 , in which , as in the embodiment according to fig4 a and 4b , magnetic flux generation means are fitted corradially into a functional coil 6 . however , in this embodiment , in two inductive sections l 1 a and l 1 b of the functional coil 6 , a first additional coil section 7 a having an inductance la , with which a capacitance ca is associated , and a second additional coil section 7 d having an inductance lb , with which a capacitance cb is associated , are inserted . in this way , two magnetic flux barriers which can be adapted separately to different frequencies are formed in the electrode line . independently thereof , the configuration of individual magnetic flux generation means distributed over the length of a functional conductor can have advantages with respect to the mechanical properties of the implant provider , in particular greater flexibility . fig6 shows , as a further embodiment , an electrode line 8 having a coiled functional conductor 9 and a further coiled section 10 , situated coaxially thereto and enclosing the functional conductor 9 , having an inductance l and an associated capacitance c . moreover , in the coaxial embodiment , the winding direction of the coil of the magnetic flux generation means can also be opposite to the winding direction of the functional conductor . fig7 shows , as a further embodiment of the invention having a particularly simple design , an electrode line 11 , in which the functional conductor 12 is provided in a section with an inductance l 1 having a coating 12 a , which implements the inductance l of a resonant circuit formed using the capacitance c as the magnetic flux generation means . the coating is applied here to the functional conductor in the form of two semicylindrical sections . fig8 shows , as an alteration , an electrode line 11 ′, in which the functional conductor 12 is provided in the relevant section with a coating 12 a ′ enclosing the entire conductor circumference . in fig9 , as a further embodiment , the internal structure of an electrode line 13 is schematically shown , the arrows a , b symbolizing a mechanical mobility of the magnetic flux generation means in relation to the functional conductor or , more precisely , the particular coil sections associated with these elements . in this way , a pitch transducer can be mechanically implemented . in particular , the mobility can be implemented like a screw - nut relationship between the coil sections , in that the inductive element l engages like a nut in the functional conductor l 1 . the capacitive element is only shown symbolically . it is advantageous if the functional conductor l 1 is moved in relation to l . fig1 shows , as an alteration of this embodiment , an electrode line 14 , in which the functional conductor 15 is movable like a screw in a thread of a nut . the internal thread is formed by a conductive structure 16 , the turns each having no lateral contact to one another . as in the embodiment according to fig4 b , a resonant circuit capacitor 17 , which sheathes the relevant section of the functional conductor 15 , is provided with an internal cylinder 17 a , an external cylinder 17 b , and a dielectric material 17 c , which is attached to the inductive element 16 of the resonant circuit of the functional conductor . fig1 shows , as a further modification , the interior of an electrode line 14 ′, in which the functional conductor 15 ′ is implemented in the screw - nut translation section as a coil section 15 a ′ having high electrical conductivity , like the “ thread section ” 16 of the magnetic flux generation means . the conductivity of the area designated in the present case as highly conductive is preferably to be more than twice as high as that of the functional conductor , i . e ., the actual electrode coil . alternatively , the functional conductor l itself can also be highly conductive . fig1 shows , in a schematic sketch oriented to fig4 a , an electrode line 1 ″ as a further embodiment , which has the same design features as the electrode line 1 according to fig4 a . however , the capacitor c of the lc resonant circuit ( the magnetic flux generation means ) is settable in its capacitance here , for example , voltage - controlled , in order to set the action frequency of the interfering signal reduction caused using the magnetic flux generation means . in a preferred embodiment , the adjustment , i . e ., the trimming of the capacitor c , occurs automatically as a function of the interfering frequency . fig1 shows a concrete implementation of this automatic adjustment of the magnetic flux generation means on the example of the electrode line 1 ″ from fig1 . the configuration shown comprises a field sensor 18 ( such as a dipole ), a frequency - voltage transducer 19 connected at the input thereto , a demodulator 20 connected at the input thereto , and finally a low - pass filter 21 , with whose output signal the capacitance of the capacitor c is controlled . a voltage divider made of two impedances , such as one resistor and one inductance , implements the frequency - voltage transducer in particular . the demodulator 20 can be implemented by a diode , and a reasonable implementation of the low - pass filter is an rc element . the voltage - dependent capacitor itself can be a capacitance diode ( varicap , varactor ), for example . fig1 shows a corresponding embodiment , the impedances z 1 , z 2 implementing the frequency - voltage transducer 19 , the diode d implementing the demodulator 20 , and rt , ct implementing the low - pass filter 21 from fig1 . the characteristic curve of the voltage - dependent capacitance is selected so that the active frequency precisely follows the frequencies of the external interfering field acquired using the field sensor 18 . alternatively , the frequency - voltage transducer can also be implemented having a corresponding compensating characteristic curve . the implementation of the invention is not restricted to the above - described examples and emphasized aspects , but rather is also possible in manifold alterations , which are within the scope of typical measures of one skilled in the art . it will be apparent to those skilled in the art that numerous modifications and variations of the described examples and embodiments are possible in light of the above teaching . the disclosed examples and embodiments are presented for purposes of illustration only . therefore , it is the intent to cover all such modifications and alternate embodiments as may come within the true scope of this invention .
implantable element having an elongate main body , a functional conductor which extends in the longitudinal direction of the main body or forms it , and which acts to implement a medical function of the element and has an inductive section , and magnetic flux generation means for generating a magnetic flux in the surroundings of the functional conductor , in particular of its inductive section , which are magnetically coupled to the functional conductor in such a way that the magnetic flux generated upon a current flux through the functional conductor is counteracted and the current flux density through the functional conductor is thus reduced .