Method and assembly for the generation of signal shapes for healing wounds by electro-stimulation

Abstract

A method for generating a signal shape (w 1 ) for an electro-stimulation signal (w 1 ) for healing wounds by electro-stimulation by way of an electrode (E 1 ) which has an encoding member ( 6 ) with a code word (cw) which identifies therapeutic treatments, and is coupled to indicators (i 1 , i 2 ) which indicate which treatments have to be activated. The signal shape (w 1 ) is formed systematically from base signals capable of being parameterized such as a DC signal and two pulse trains, the parameters and the timing of which are formed systematically and applied where necessary, in accordance with the combined therapies. The generation of signal shapes for a plurality of electrodes is also disclosed.

1 . A method for generating a signal shape (w 1 ) of an electro-stimulation signal to be supplied to an electrode (E 1 ) for healing wounds by electro-stimulation, the method comprises the following steps:
 a) the connection of an electrode (E 1 ) to a signal shape generator ( 23 ), wherein the electrode (E 1 ) is connected to an encoding member ( 6 ) in which a code word (cw) is stored, wherein the code word (cw) comprises at least two code word portions (c 1 , c 2 , . . . ), and wherein each code word portion identifies a respective therapeutic treatment (tb 1 , tb 2 , . . . ), and wherein each code word portion haves coupled to them a respective indicator (i 1 , i 2 , . . . ) indicating whether the therapeutic treatment (tb 1 , tb 2 , . . . ) associated with the respective code word portion should be activated or not;   b) the retrieval from the encoding member ( 6 ) of the code word portions (c 1 , c 2 , . . . ) and the associated indicators (i 1 , i 2 , . . . );   c) checking whether a first indicator (i 1 ) coupled to a first code word portion (c 1 ) of the retrieved code word portions indicates activation,
 and if the first indicator (i 1 ) indicates activation, the retrieval of a first signal (s 1 ) associated with the therapeutic treatment (tb 1 ) identified by the first code word portion and the formation of a temporary signal shape (w) on the basis of the first signal (s 1 ), 
 and if the first indicator (i 1 ) does not indicate activation, passing on to step d); 
   d) for each further code word portion (c 2 , c 3 , . . . ) of the retrieved code word portions, checking each time whether the further indicator (i 2 , i 3 , . . . ) which is coupled to the further code word portion (c 2 , c 3 , . . . ) indicates activation,
 and each time if the further indicator (i 2 , i 3 , . . . ) indicates activation and the temporary signal shape (w) is formed, the retrieval of a further signal (s 2 , s 3 , . . . ) associated with the further therapeutic treatment (tb 2 , tb 3 , . . . ) identified by the considered further code word portion (c 2 , c 3 , . . . ), and the further formation of the temporary signal shape (w) on the basis of the temporary signal shape (w) and the further signal (s 2 , s 3 , . . . ), 
 and each time if the further indicator (i 2 , i 3 , . . . ) indicates activation and the temporary signal shape (w) is not yet formed, the retrieval of a further signal (s 2 , s 3 , . . . ) associated with the further therapeutic treatment (tb 2 , tb 3 , . . . ) identified by the considered further code word portion (c 2 , c 3 , . . . ), and the formation of the temporary signal shape (w) on the basis of the further signal (s 2 , s 3 , . . . ), 
 and each time if the further indicator (i 2 , i 3 , . . . ) does not indicate activation and the signal shape (w) is formed, the maintaining of the temporary signal shape (w); 
   e) the generation of the signal shape (w 1 ) on the basis of the temporary signal shape (w) after all the further code word portions have been treated;   characterized in that before said signal shape is generated the temporary signal shape is checked in order to establish whether or not the temporary signal shape falls within therapeutic limits of the therapeutic treatments identified by each of the signals on which the temporary signal shape was formed, said temporary signal shape being adjusted so as to fall within said therapeutic limits if it has been established that it did not fall within said therapeutic limits.   
     
     
         2 . The method according to  claim 1 ,
 wherein the first signal (s 1 ) is a first DC signal with a first DC value (D 1 ), and wherein the further signal is a second DC signal (s 2 ) with a second DC value (D 2 );   and wherein the temporary signal shape (w) is formed by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (i 2 ) does indicate activation;   and wherein the adjustment of the temporary signal shape (w) on the basis of the first DC signal (s 1 ) and the second DC signal (s 2 ) comprises changing the first DC value (D 1 ) to a third DC value (D) lying in a range with the first DC value (D 1 ) and the second DC value (D 2 ) as the limit values.   
     
     
         3 . The method according to  claim 2 , wherein the adjustment of the first DC value (D 1 ) is setting the first DC value (D 1 ) equal to the smallest DC value of the first DC value and the second DC value (D 1 , D 2 ). 
     
     
         4 . The method according to  claim 1 ,
 wherein the first signal (s 1 ) is a first DC signal with a first DC value (D 1 ), and wherein the further signal is a second signal (s 2 ) formed by a first pulse train (PT 1 ) with a first frequency (f 1 ) lower than a predetermined frequency (fv) and with a first pulse amplitude (A 1 ) and with a first pulse width (B 1 );   and wherein the temporary signal shape (w) is formed by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (s 2 ) does indicate activation;   and wherein the adjustment of the temporary signal shape (w) on the basis of the first DC signal (s 1 ) and the first pulse train (PT 1 ) comprises splitting the first period (Tact 1 ) into at least one first and at least one second period portion (P 1 , P 2 ), wherein the first DC value (D 1 ) is maintained during the at least one first period portion (P 1 ), and wherein the first DC value (D 1 ) is reduced to a reduced DC value (D 1 *) during the at least one second period portion (P 2 ), and the first pulse amplitude (A 1 ) is reduced to a reduced first pulse amplitude (A 1 *), and the first pulse train (PT 1 ) with the reduced first pulse amplitude (A 1 *) is superimposed upon the first DC signal with the reduced DC value (D 1 *).   
     
     
         5 . The method according to  claim 1 ,
 wherein the first signal (s 1 ) is a first DC signal with a first DC value (D 1 ), and wherein the further signal is a second signal (s 2 ) having a second pulse train (PT 2 ) with a second frequency (f 2 ) higher than the previously defined frequency (fv) and with a second pulse amplitude (A 2 ) and with a second pulse width (B 2 );   and wherein the temporary signal shape (w) is formed by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (i 2 ) does indicate activation;   and wherein the adjustment of the temporary signal shape (w) on the basis of the first DC signal (s 1 ) and the second pulse train (PT 2 ) comprises splitting the first period (Tact 1 ) into a plurality of period portions (P 1 ), and the fractioning of each period portion (P 1 ) into a first and a second period fraction (P 1   a , P 1   b ), wherein the DC signal with the first DC value (D 1 ) is maintained during the first period fraction (P 1   a ), and wherein the second pulse amplitude (A 2 ) is reduced to a reduced second pulse amplitude (A 2 *) during the second period fraction (P 1   b ), and the DC signal is replaced by the second pulse train (PT 2 ) with the reduced second pulse amplitude (A 2 *).   
     
     
         6 . The method according to  claim 4 , wherein the predetermined frequency (fv) is a frequency in the range of from 20 to 50 Hz, preferably substantially equal to 30 Hz. 
     
     
         7 . The method according to  claim 6 , wherein the period portion (P 1 ) is fractioned into the first period fraction (P 1   a ) with a first fraction duration (Ta) and into the second period fraction (P 1   b ) with a second fraction duration (Tb), wherein the ratio of the second fraction duration (Tb) and the first fraction duration (Ta) is a ratio of from 10/90 to 40/60, preferably substantially equal to 20/80. 
     
     
         8 . The method according to  claim 1 ,
 wherein the first signal (s 1 ) is a first pulse train (PT 1 ) with a first frequency (f 1 ) lower than the predetermined frequency (fv) and with a first pulse amplitude (A 1 ) and with a first pulse width (B 1 ), and wherein the further signal is a second signal (s 2 ) having a second pulse train (PT 2 ) with a second frequency (f 2 ) higher than the predetermined frequency (fv) and with a second pulse amplitude (A 2 ) and with a second pulse width (B 2 );   and wherein the temporary signal shape (w) is formed by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (s 2 ) does indicate activation;   and wherein the adjustment of the temporary signal shape (w) on the basis of the first pulse train (PT 1 ) and the second pulse train (PT 2 ) comprises splitting the first period (Tact 1 ) into a plurality of period portions (P 1 ), and the fractioning of each period portion (P 1 ) into a plurality of first and second period fractions (P 1   a , P 1   b ), wherein the first pulse train (PT 1 ) with the first pulse amplitude (A 1 ) is maintained during the first period fraction (P 1   a ), and wherein the first pulse train is replaced by the second pulse train (PT 2 ) during the second period fraction (P 1   b ).   
     
     
         9 . The method according to  claim 1 ,
 wherein the code word (cw) comprises at least three code word portions (c 1 , c 2 , c 3 ), and wherein the second and third code word portion (c 3 ) respectively identifies a second and a third therapeutic treatment (tb 3 ), and wherein the second and third code word portion (c 2 , c 3 ) has coupled to it a second (i 2 ) respectively a third indicator (i 3 ) which indicates whether the second respectively the third therapeutic treatment (tb 3 ) should be activated or not;   and wherein the first signal (s 1 ) is a first DC signal with a first DC value (D 1 ), and wherein the second signal (s 2 ) is a first pulse train (PT 1 ) with a first frequency (f 1 ) lower than the predetermined frequency (fv) and with a first pulse amplitude (A 1 ) and with a first pulse width (B 1 ), and wherein the third signal (s 3 ) is a second pulse train (PT 2 ) with a second frequency (f 2 ) higher than the predetermined frequency (fv) and with a second pulse amplitude (A 2 ) and with a second pulse width (B 2 );   and wherein the temporary signal shape (w) is formed by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (s 2 ) does indicate activation, and by taking the third signal (s 3 ) over the first period (Tact 1 ) if the first and the second indicators (i 1 , i 2 ) do not indicate activation and the third indicator does indicate activation;   and wherein the adjustment of the temporary signal shape (w) with the first DC signal (s 1 ) and the first pulse train (PT 1 ) comprises splitting the first period (Tact 1 ) into at least one first and at least one second period portions (P 1 , P 2 ), wherein the first DC value (D 1 ) is maintained during the at least one first period portion (P 1 ), and wherein the first DC value (D 1 ) is reduced to a reduced DC value (D 1 *) during the at least one second period portion (P 2 ), and the first pulse amplitude (A 1 ) is reduced to a reduced first pulse amplitude (A 1 *), and the first pulse train (PT 1 ) with the reduced first pulse amplitude (A 1 *) is superimposed upon the first DC signal with the reduced DC value (D 1 *);   and wherein adjustment of the temporary signal shape (w) with the first DC signal (s 1 ) and the second pulse train (PT 2 ) comprises splitting the first period (Tact 1 ) into a plurality of period portions (P 1 ), and the fractioning of each period portion (P 1 ) into a first and a second period fraction (P 1   a , P 1   b ), wherein the first DC value (D 1 ) is maintained during the first period fraction (P 1   a ), and wherein the second pulse amplitude (A 2 ) is reduced to a reduced second pulse amplitude (A 2 *) during the second period fraction (P 1   b ), and the DC signal is replaced by the second pulse train (PT 2 ) with the reduced second pulse amplitude (A 2 *);   and wherein the adjustment of the temporary signal shape (w) with the first pulse train (PT 1 ) and the second pulse train (PT 2 ) comprises splitting the first period (Tact 1 ) into a plurality of period portions (P 1 ), and the fractioning of each period portion (P 1 ) into a first and a second period fraction (P 1   a , P 1   b ), wherein the first pulse train (PT 1 ) is maintained during the first period fraction (P 1   a ), and the first pulse train (PT 1 ) is replaced by the second pulse train (PT 2 ) during the second period fraction (P 1   b );   and wherein the further forming of the temporary signal shape (w) on the basis of the first DC signal (s 1 ) and with the first pulse train (PT 1 ) and the second pulse train (PT 2 ) comprises in a first step splitting the first period (Tact 1 ) into a first and a second period portion (P 1 , P 2 ), wherein the first DC value (D 1 ) is maintained during the first period portion (P 1 ), and wherein the first DC value (D 1 ) is reduced to a reduced DC value (D 1 *) during the second period portion (P 2 ), and the first pulse amplitude (A 1 ) is reduced to a reduced first pulse amplitude (A 1 *), and the first pulse train (PT 1 ) with the reduced first pulse amplitude (A 1 *) is superimposed upon the first DC signal with the reduced DC value (D 1 *), and in a second step the fractioning of the first period portion (P 1 ) into a plurality of first and second period fractions (P 1   a , P 1   b ), wherein the DC signal with the first DC value (D 1 ) is maintained during each first period fraction (P 1   a ), and the second pulse amplitude (A 2 ) is reduced to a reduced second pulse amplitude (A 2 *) during each second period fraction (P 1   b ), and the DC signal is replaced by the second pulse train (PT 2 ) with the reduced second pulse amplitude (A 2 *), and the splitting of the second period portion (P 2 ) into a plurality of third and fourth period fractions (P 2   a , P 2   b ), wherein the DC signal with the reduced DC value (D 1 *) with the first pulse train (PT 1 ) with the reduced first pulse amplitude (A 1 *) superimposed upon it is maintained during each third period fraction (P 2   a ), and the second pulse amplitude (A 2 ) is reduced to a reduced second pulse amplitude (A 2 *) during each fourth period fraction (P 2   b ), and the DC signal with the reduced DC value (D*) with the first pulse train (PT 1 ) with the reduced first pulse amplitude (A 1 *) superimposed upon it is replaced by the second pulse train (PT 2 ) with the reduced second pulse amplitude (A 2 *).   
     
     
         10 . The method according to  claim 9 , wherein the first and the second pulse train (PT 1 , PT 2 ) are selected in such a way that the second frequency (f 2 ) of the second pulse train (PT 2 ) is an integral multiple of the first frequency (f 1 ) of the first pulse train (PT 1 ). 
     
     
         11 . The method according to  claim 9 , wherein the code word comprises at least four code word portions (c 1 , c 2 , c 3 , c 4 ), wherein the first code word portion (c 1 ) identifies an antibacterial treatment, the second code word portion (c 2 ) identifies a cell migration treatment, the third code word portion (c 3 ) identifies a treatment for pain and/or a treatment for the increase in the oxygen tension TcPO2, and the fourth code word portion (c 4 ) identifies a stimulation of one or more processes selected from the group of ATP production, DNA production, protein production and amino acid absorption. 
     
     
         12 . The method according to  claim 1 , wherein one of the code word portions (c 1 ) identifies an antibacterial treatment as an associated therapeutic treatment (tb 1 ), and wherein a DC signal with a DC value (D 1 ) of from 4 to 750 μA, preferably from 300 to 500 μA, and in a more preferable manner approximately 400 μA, is selected as the signal (s 1 ) associated with this therapeutic treatment (tb 1 ). 
     
     
         13 . The method according to  claim 1 , wherein one of the code word portions (c 2 ) identifies a cell migration treatment as an associated therapeutic treatment (tb 2 ), and wherein a DC signal with a DC value (D 2 ) of from 50 to 750 μA, preferably approximately 100 μA, is selected as the signal (s 2 ) associated with this therapeutic treatment (tb 2 ). 
     
     
         14 . The method according to  claim 1 , wherein one of the code word portions (c 3 ) identifies a treatment for pain and/or a treatment for the increase in the oxygen tension TcPO2 as an associated therapeutic treatment (tb 3 ), and wherein a first pulse train (PT 1 ) with a first frequency (f 1 ) of from 0.2 to 20.0 Hz, preferably approximately 5.0 Hz, and with a first pulse amplitude (A 1 ) of from 10 to 750 μA, preferably from 100 to 400 μA, and with a first pulse width (B 1 ) of from 0.1 to 20 ms, preferably from 1.0 to 3.0 ms, is selected as the signal (s 3 ) associated with this therapeutic treatment (tb 3 ). 
     
     
         15 . The method according to  claim 1 , wherein one of the code word portions (c 4 ) identifies a stimulation of a process selected from the group of ATP production, DNA production, protein production and amino acid absorption as an associated therapeutic treatment (tb 4 ), and wherein a second pulse train (PT 2 ) with a second frequency (f 2 ) of from 50 to 160 Hz, preferably approximately 100 Hz, and with a second pulse amplitude (A 2 ) of from 10 to 750 μA, preferably from 100 to 400 μA, and with a second pulse width (B 2 ) of from 0.1 to 5.0 ms, preferably from 0.2 to 2.0 ms, is selected as the signal (s 4 ) associated with this therapeutic treatment (tb 4 ). 
     
     
         16 . The method according to  claim 1 , wherein a period of rest (Trust) is introduced after the first period (Tact 1 ), wherein a DC signal with a DC value (D) substantially equal to zero is assigned to the signal shape (w 1 ), and wherein after the period of rest (Trust) the first period (Tact 1 ) and the period of rest (Trust) are periodically repeated. 
     
     
         17 . A method of generating a group (G 1 ) of signal shapes (w 1 , w 2 , w 3 ) from an electro-stimulation signal to be provided at the same time to a plurality of electrodes (E 1 , E 2 , E 3 ) for healing wounds by electro-stimulation, characterized in that the method comprises the following steps:
 f) checking whether a first electrode (E 1 ) is connected to the signal shape generator ( 23 ), and if the first electrode (E 1 ) is connected, generating a first signal shape (w 1 ) for the first electrode (E 1 ) according to  claim 6 ;   g) repeatedly checking whether a further electrode (E 2 , E 3 ) is connected to the signal shape generator ( 23 ), and if the further electrode (E 2 , E 3 ) is connected, generating a further signal shape (w 2 , w 3 ) for the further electrode (E 2 , E 3 ) according to  claim 6 , wherein the duration of the first period (Tact 1 ), the duration of the first and the second period portion (P 1 , P 2 ) respectively and the duration of the first and the second, third and fourth period fractions (P 1   a , P 1   b , P 2   a , P 2   b ) respectively of the further signal shape (w 2 , w 3 ) is selected to be the same as those of the first signal shape (w 1 );   h) checking, for each first period (Tact 1 ) and period portion (P 1 , P 2 ) and period fraction (P 1   a , P 1   b , P 2   a , P 2   b ) of the signal shapes (w 1 , w 2 , w 3 ), whether a plurality of pulse trains (PT 1 , PT 2 ) occur simultaneously, and, if a plurality of pulse trains occur simultaneously, defining a shift (d 1 , d 2 ) for each pulse train of each signal shape (w 1 , w 2 , w 3 ) in such a manner that the pulses of the pulse trains do not overlap in time after shifting over the shifts, and associating the shifts (d 1 , d 2 ) with the period and period portion and period fractions with the simultaneous pulse train;   i) checking, for each first period (Tact 1 ) and period portion (P 1 , P 2 ) and period fraction (P 1   a , P 1   b , P 2   a , P 2   b ) of the signal shapes (w 1 , w 2 , w 3 ), whether a plurality of DC signals occur simultaneously, and, if a plurality of DC signals occur simultaneously, calculating a first sum (Σ 1 ) of the DC values (D) of the DC signals occurring simultaneously, and if this first sum (Σ 1 ) is greater than a first maximum value (M 1 ), calculating a first scale factor (α) as a proportion of the first sum (Σ 1 ) and the first maximum value (M 1 ), and associating the first scale factor (α) with the period and period portion and period fraction with the simultaneous DC signal;   j) checking, for each first period (Tact 1 ) and period portion (P 1 , P 2 ) and period fraction (P 1   a , P 1   b , P 2   a , P 2   b ) of the signal shapes (w 1 , w 2 , w 3 ), whether at least one DC signal and at least one pulse train (PT 1 , PT 2 ) occur simultaneously, and if at least one DC signal and at least one pulse train occur simultaneously, calculating a DC component (AG 1 , AG 2 ) of each simultaneous pulse train by multiplication of the pulse amplitude (A 1 , A 2 ) and the averaged duty cycle of the pulse train, and calculating a second sum (Σ 2 ) of the DC values (D) and the DC components (AG 1 , AG 2 ) of the simultaneously occurring DC signals and pulse trains, and, if the second sum is greater (Σ 2 ) than a second maximum value (M 2 ), limiting the DC values (D) which are greater than a limiting value (K) to the limiting value (K), and associating the limiting value (K) to the period and period portion and period fraction with the simultaneous DC signal with a DC value greater than the limiting value (K), and recalculating the second sum whilst taking into consideration the limited DC values, and, if the recalculated second sum (Σ 2 ′) is greater than the second maximum value (M 2 ), calculating a second scale factor (β) as a proportion of the recalculated second sum (Σ 2 ′) and the second maximum value (M 2 ), and associating the second scale factor (β) with the period and period portion and period fraction with the simultaneously occurring DC value or pulse train;   k) repeating the steps g) to j) inclusive for each further electrode (E 2 , E 3 ), and adding the further signal shape (w 2 , w 3 ) to the group (G 1 );   m) checking, for each first period (Tact 1 ) and period portion (P 1 , P 2 ) and period fraction (P 1   a , P 1   b , P 2   a , P 2   b ) of the signal shapes (w 1 , w 2 , w 3 ), whether at least one shift (d 1 , d 2 ) or at least one limiting value (K) or at least one scale factor (α, β) is associated with the first period and period portion and period fraction, and, if at least one shift or limiting value or scale factor is associated, adapting the signal shapes (w 1 , w 2 , w 3 ) of the group (G 1 ) in each first period (Tact 1 ) and period portion (P 1 , P 2 ) and period fraction (P 1   a , P 1   b , P 2   a , P 2   b ),
 by checking whether the shift (d 1 , d 2 ) is associated with the first period or period portion or period fraction, and, if the shift (d 1 , d 2 ) is associated, shifting the pulse train (PT 1 , PT 2 ) over the associated shift, 
 and by checking whether the limiting value (K) is associated with the first period or period portion or period fraction, and, if the limiting value (K) is associated, limiting the DC values (D) greater than the limiting value (K) to the limiting value (K), 
 and by checking whether the first scale factor (α) is associated with the first period or period portion or period fraction, and, if the first scale factor (α) is associated, scaling the DC values with the first scale factor (α), 
 and by checking whether the second scale factor (α) is associated with the first period or period portion or period fraction, and, if the second scale factor (α) is associated, scaling the limited DC values (D, K) and the pulse amplitudes (A 1 , A 2 ) with the second scale factor (β). 
   
     
     
         18 . The method according to  claim 17 , wherein
 in step h) a further test is made into whether the defined shift (d 1 , d 2 ) is greater than a predetermined maximum shift (dmax 1 , dmax 2 ),   and wherein in step i) a further test is made into whether the DC value (D) scaled with the first scale factor (α) of at least one signal shape is smaller than a first minimum value (m 1 );   and wherein in step j) a further test is made into whether the pulse amplitude (A) scaled with the second scale factor (Q) of at least one signal shape is smaller than a second minimum value (m 2 );   and if one of these tests is met, removing at least one signal shape from the first group (G 1 ), and recalculating the signal shapes of the first group (G 1 ), and forming a second group (G 2 ) according to  claim 17  for the remaining signal shapes,   and wherein the signal shapes of the first and the second group (G 1 , G 2 ) are shifted with respect to one another in such a way that the signal shapes (w 1  to w 4 ) of the first group (G 1 ) are active in a first active period (Tact 1 ) in which the signal shapes (w 5 , w 6 ) of the second group (G 2 ) are at rest, and wherein the signal shapes (w 5 , w 6 ) of the second group (G 2 ) are active in a second active period (Tact 2 ) which does not overlap with the first active period and wherein the signal shapes (w 1  to w 4 ) of the first group (G 1 ) are at rest.   
     
     
         19 . An assembly ( 1 ) for healing wounds by electro-stimulation, comprising:
 at least one electrode (E 1 ) which is connected to an encoding member ( 6 ) in which a code word (cw) has been stored, wherein the code word (cw) comprises at least two code word portions (c 1 , c 2 , . . . ), and wherein each code word portion identifies a respective therapeutic treatment (tb 1 , tb 2 , . . . ) respectively, and wherein each code word portion have coupled to them a respective indicator (i 1 , i 2 , . . . ) which indicates whether the therapeutic treatment (tb 1 , tb 2 , . . . ) associated with the code word portion in question should be activated or not;   an electronic apparatus ( 2 ) with at least one port ( 5 ) for connecting the apparatus ( 2 ) to the electrode (E 1 ),   and with a data-processing unit ( 3 ) connected to the port for retrieving the code word (cw) from the encoding member ( 6 ), and for determining the associated therapeutic treatments (tb 1 , tb 2 , . . . ) on the basis of the code word portions (c 1 , c 2 , . . . ) and for checking the activation of the indicators (i 1 , i 2 , . . . ),   and with a signal shape generator ( 23 ) with a memory for retrieving each time a signal (s 1 , s 2 , . . . ) associated with the therapeutic treatment (tb 1 , tb 2 , . . . ) identified by the considered code word portion, said signal shape generator being provided for forming a temporary signal shape (w) on the basis of the retrieved signals, said signal shape generator comprising a buffer for storing said temporary signal shape (w),   and with a clock circuit for the generation of the signal shape (w 1 ),   
       characterized in that said signal shape generator is provided with checking means provided for checking whether or not said temporary signal shape (w) falls within therapeutic limits of the therapeutic treatment identified by the considered code word portions, and for adjusting said temporary signal shape (w) when it does not fall within said therapeutic limits to a signal shape falling within said therapeutic limits. 
     
     
         20 . The assembly ( 1 ) according to  claim 19 , wherein the electrode (E 1 ) has a connector ( 4 ) which comprises the encoding member ( 6 ), and wherein the electronic apparatus ( 2 ) further comprises at least one port ( 5 ) for receiving the connector ( 4 ). 
     
     
         21 . The assembly ( 1 ) according to  claim 19 ,
 wherein a first signal (s 1 ) of said signals is a first DC signal with a first DC value (D 1 ), and wherein a second of said signals is a second DC signal (s 2 ) with a second DC value (D 2 );   and wherein said signal shape generator is provided for forming the temporary signal shape (w) by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact) if the first indicator (i 1 ) does not indicate activation and the second indicator (i 2 ) does indicate activation;   and wherein said signal shape generator is provided for applying the adjustment of the temporary signal shape (w) on the basis of the first DC signal (s 1 ) and the second DC signal (s 2 ) comprises changing the first DC value (D 1 ) to a third DC value (D) lying in a range with the first DC value (D 1 ) and the second DC value (D 2 ) as the limit values.   
     
     
         22 . The assembly ( 1 ) according to  claim 19 , wherein
 a first signal (s 1 ) of said signals is a first DC signal with a first DC value (D 1 ), and wherein a second of said signals is a second signal (s 2 ) formed by a first pulse train (PT 1 ) with a first frequency (f 1 ) lower than a predetermined frequency (fv) and with a first pulse amplitude (A 1 ) and with a first pulse width (B 1 );
 and wherein said signal shape generator is provided for forming the temporary signal shape (w) by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (s 2 ) does indicate activation; 
 and wherein said signal shape generator is provided for forming the adjustment of the temporary, signal shape (w) on the basis of the first DC signal (s 1 ) and the first pulse train (PT 1 ) comprises splitting the first period (Tact 1 ) into at least one first and at least one second period portion (P 1 , P 2 ), wherein the first DC value (D 1 ) is maintained during the at least one first period portion (P 1 ), and wherein the first DC value (D 1 ) is reduced to a reduced DC value (D 1 *) during the at least one second period portion (P 2 ), and the first pulse amplitude (A 1 ) is reduced to a reduced first pulse amplitude (A 1 *), and the first pulse train (PT 1 ) with the reduced first pulse amplitude (A 1 *) is superimposed upon the first DC signal with the reduced DC value (D 1 *). 
   
     
     
         23 . The assembly ( 1 ) according to  claim 19 ,
 wherein a first of said signals signal (s 1 ) is a first DC signal with a first DC value (D 1 ), and wherein a second of said signals is a second signal (s 2 ) having a second pulse train (PT 2 ) with a second frequency (f 2 ) higher than the previously defined frequency (fv) and with a second pulse amplitude (A 2 ) and with a second pulse width (B 2 );
 and wherein signal shape generator forms the temporary signal shape (w) by taking the first signal (s 1 ) over a first period (Tact 1 ) if the first indicator (i 1 ) indicates activation, and by taking the second signal (s 2 ) over the first period (Tact 1 ) if the first indicator (i 1 ) does not indicate activation and the second indicator (i 2 ) does indicate activation; 
 and wherein the adjustment of the temporary signal shape (w) on the basis of the first DC signal (s 1 ) and the second pulse train (PT 2 ) comprises splitting the first period (Tact 1 ) into a plurality of period portions (P 1 ), and the fractioning of each period portion (P 1 ) into a first and a second period fraction (P 1   a , P 1   b ), wherein the DC signal with the first DC value (D 1 ) is maintained during the first period fraction (P 1   a ), and wherein the second pulse amplitude (A 2 ) is reduced to a reduced second pulse amplitude (A 2 *) during the second period fraction (P 1   b ), and the DC signal is replaced by the second pulse train (PT 2 ) with the reduced second pulse amplitude (A 2 *). 
   
     
     
         24 . The electronic apparatus ( 2 ) as an element of the assembly ( 1 ) according to  claim 19 , wherein the electronic apparatus further comprises a battery ( 36 ) for the delivery of energy, and a micro-current module ( 37 ) connected to the signal shape generator ( 23 ) for the generation of an electro-stimulation signal (i 1 ) to be supplied to the electrode (E 1 ) on the basis of the signal shape (w 1 ) generated.