EP3010584A1 - Magnetic stimulator for stimulating tissue with a magnetic field - Google Patents

Abstract

The invention relates to a magnetic stimulator for stimulating tissue with a magnetic field, comprising a pulse generator device which has a pulse capacitor that can be charged by a charging circuit for generating a pulse sequence, which consists of pulses, with an adjustable repetition rate; and a programmable control device which controls the pulse generator device to generate a complex pulse sequence having individually configurable pulses, the generated complex pulse sequence being applied to a stimulation coil to generate the magnetic field.

Description

Magnetic stimulator for stimulating a tissue through a magnetic field

Magnetic stimulation can be used for the non-invasive examination and stimulation of tissue, in particular organic tissue. In this case, an alternating magnetic field is he witnesses ^¬ by means of a short current ^¬ flow through a coil. With transcranial magnetic stimulation (TMS), for example, the human brain is stimulated by the applied alternating magnetic field. By the stimulation, for example, motor brain areas motor evoked potentials (MEP) can be derived in muscle tissue, allowing their own ^¬ properties and changes conclusions on the excitability of the examined brain areas. TMS is of particular importance in the induction and evaluation of cortical plasticity. Cortical plasticity concerns the ability of the brain to adapt to changing conditions. Further, a repetitive stimulation by a magnetic field can ^¬ tables pulse gen in the therapy of various Erkrankun-, in particular depression, may be used. For evalua ^¬ tion of the corticospinal system transcranial Mag ^¬ netstimulation is used because of its high sensitivity and relatively simple feasibility regularly for neurological diagnosis. Through the application of stimulation protocols of transcranial magnetic stimulation, both the influence and the evaluation of the function of neural networks can take place.

The alternating magnetic field generated by a stimulation coil can excite motor neurons of the tissue to a motor-evoked potential and to an accompanying muscle response. This motor evoked potential Poten ^¬ can be derived and analyzed. The stimulus tion induced field used is generated by means of a pulsed magnetic field, and this can be applied to the contactless Pa ^¬ tienten and there causes no pain.

Conventional magnetic stimulators use a resonant circuit for generating the alternating magnetic field. This resonant circuit comprises a pulse capacitor and a Stimulationssspu ^¬ le. Fig. 1 shows a conventional magnetic stimulator, as described in DE 10 2006 024 467 AI. This magnetic stimulator contains a resonant circuit with a Pulskondensa ^¬ tor C and a stimulation coil for generating a magnetic ^¬ field. A charging circuit is provided for charging the Pulskondensa ^¬ sector C. In addition, the conventional in Fig. 1 magnetic stimulator includes a controllable switch for interrupting and closing the resonant circuit. A control ^¬ circuit opens and closes the controllable switch such that a stimulation pulse with egg ^¬ ner an adjustable number of half or full waves can be generated by the resonant circuit. The controllable switch may be, for example, a thyristor or an IGBT. With the help of the controllable switch integer multiples of full waves can be applied. Before the pulse is triggered, the pulse capacitor is charged to a desired voltage. The energy content of the pulse capacitor sets the current determined by the Stimula ^¬ tion coil and thus the pulse intensity (pulse strength) of the ex ^¬ be played pulse. When the switch is closed, a current begins to flow through the stimulation coil and the pulse capacitor begins to discharge. After the coil current has decayed, the entire pulse energy is consumed and the pulse capacitor is completely discharged. The pulse capacitor must be recharged to the desired voltage level before the next pulse. Such conventional However, magnetic stimulators have the disadvantage that the number of pulses generated by the pulse generator means is limited in time. In conventional magnetic stimulators, the maximum repetition rate, ie the number of pulses delivered per time, is 100 pulses per second. Another disadvantage of conventional magnetic stimulators wesentli ^¬ cher is that these are merely sinusoidal pulses can produce. Conventional magnetic stimulators usually generate monophasic and biphasic pulses with adjustable pulse width. In addition, with conventional magnetic stimulators only pulse sequences can be generated, which contain pulses of the same pulse shape. An individual configuration of the pulses in terms of their pulse shape and / or pulse polarity to build complex pulse sequences is not possible. An individual or flexible adaptation of the generated pulse sequence to the tissue to be examined or a clinical picture can therefore not occur in conventional magnetic stimulators.

It is therefore an object of the present invention to provide a magnetic stimulator for stimulation of a tissue by a magnetic field, in which the above mentioned disadvantages are avoided and is flexibly adaptable to the examined tissue or of a disease of a patien ^¬ th at the pulse sequences.

This object is achieved by a Magnetstimula ^¬ tor with the features specified in claim 1.

The invention accordingly provides a magnetic stimulator for stimulating a tissue through a magnetic field

a pulse generator device having a pulse capacitor, which is provided by a charging circuit for generating a pulse sequence consisting of pulses with an adjustable Repetierrate is charged and with a programmable controller, which sets the pulse generator means for generating a complex pulse sequence having individually configurable pulses,

wherein the generated complex pulse sequence is applied to a Stimulati ^¬ onsspule for generating the magnetic field.

The magnetic stimulator according to the invention makes it possible to generate complex pulse sequences and pulse patterns at a high adjustable repetition rate and to emit a stimulation coil connected to the magnetic stimulator for generating the alternating magnetic field. This allows reproducible and effective plasticity changes in a stimulated brain.

In one possible embodiment of the magnetic stimulator according to the invention, the pulse sequence output by the pulse generator means is a simple pulse sequence consisting of pulses or a complex pulse sequence.

The generated pulse frequency complex preferably has ^¬ pulse trains on each comprising pulse packets, each of which consist of a sequence of pulses wherein a pulse shape and / or polarity of the pulses is individually configurable.

In a further possible embodiment of the magnetic stimulator of the present invention the programmable Steuerein ^¬ direction of the magnetic stimulator via an interface to ei ^¬ NEN host is connected, to which a user Editor about the configuration of the pulse sequence is provided.

In a further possible embodiment of the magnetic stimulator according to the invention, the user editor of the to the Magnetic stimulator computer connected to a stimulus designer for configuring a pulse shape of the respective pulses of the pulse sequence on. In another possible embodiment, the user editor further comprises a pulse packet assistant for configuring at least one pulsed pulse packet.

In another possible embodiment, the user editor additionally has a pulse-width assistant for configuring at least one pulse train consisting of pulse packets.

In a further possible embodiment of the magnetic stimulator according to the invention, the complex pulse sequence configured by means of the user editor is transmitted via the interface to the programmable control device of the magnetic stimulator and stored in a memory unit of the magnetic stimulator.

In a further possible embodiment of the magnetic stimulator according to the invention is the repetition rate of the Pulsse ^acid sequence that specifies the number of pulses per second output pulses set in a range from 0 up to 1 kHz.

In a further possible embodiment of the magnetic stimulator according to the invention, an evaluation pulse for measuring a motor muscle response of the stimulated tissue is delivered between pulse packets of the complex pulse sequence which is generated by the pulse generator device of the magnetic stimulator. In a further possible embodiment of the magnetic stimulator according to the invention, the pulse generator means of the magnetic stimulator comprises a resonant circuit which the

Pulse capacitor and the stimulation coil includes, and at least one power switch, which is connected to a controllable by the programmable controller of the magnetic stimulator driver circuit.

In a possible embodiment of the magnetic stimulator according to the invention, the stimulation coil is connected in a Vollbrü ^¬ bridge with four power switches for the generation of pulses, the pulse shape of the pulse segments is assembled. In a further possible embodiment of the magnetic stimulator according to the invention, the pulse generator device of the magnetic stimulator has a charging circuit for recharging the pulse capacitor with the set repetition rate. In a possible embodiment of the invention

Magnetic stimulator is the charging circuit of the pulse generator means a linear charging circuit.

This linear charging circuit, in one possible exemplary form a power supply unit for connection to a power supply ^¬ net,

an intermediate power circuit for temporarily storing the electrical energy supplied by the power supply and

a charge controller, which is connected to the resonant circuit of the pulse generator device.

In a further possible alternative embodiment of the magnetic stimulator according to the invention, the charging circuit the pulse generator means a clocked charging circuit.

In a possible embodiment of the clocked charging circuit, the latter has a power supply unit for connection to a Stromver sorgungsnet ^¬ z,

a first DC / DC switching regulator for continuous operation,

a power link for latching the electrical power supplied by the first DC / DC switching regulator and

a second DC / DC switching regulator for a pulse operation, which is connected to the resonant circuit of the pulse generator means.

In a further possible embodiment of the magnetic stimulator according to the invention, the pulse generator device has a coil monitoring circuit. In one possible embodiment of the coil monitoring circuit, it monitors whether a stimulation coil is connected to the magnetic stimulator.

In a further possible embodiment of the magnetic stimulator according to Inventions, the coil supervision scarf ^¬ tung sensors for monitoring operating parameters of the stimulation coil, in particular the operating temperature, on.

In a further possible embodiment of the inventive magnetic stimulator causes the programmable

Control means the pulse generator means for delivering the pulse sequence to the stimulation coil only after a sys- temüberprüfung of parameters of the magnetic stimulator successfully completed ^¬ rich.

In a further possible embodiment of the magnetic stimulator of invention according to the programmable Steuerein ^¬ direction is connected to a attached to the tissue to be stimulated up electrode for deriving a measurement signal and / or for generating a trigger signal. In a further possible embodiment of the magnetic stimulator according to the invention, the measuring signal derived by the deflecting electrode is evaluated by the programmable control ^device for determining a motor threshold.

The invention further provides a method for generating a magnetic field having the features specified in claim 17. The invention accordingly provides a method for generating a magnetic field with the steps:

 Generating a complex pulse sequence, which consists of individually configured pulses with a variable pulse shape, by a pulse generator device,

Applying the generated pulse sequence with an adjustable repetition rate of stimulation coil which generates therefrom the Mag ^¬ netfeld and

 Recharging a pulse capacitor of the pulse generator means by a charging circuit with the set Repetierrate.

In a possible embodiment of the method according to the invention, the repetition rate, which is the number of pulses indicates per time, in a range from 0 to 1 kHz turned ^¬ adjusted.

In one possible embodiment of the method according to the invention, the generated complex pulse sequence has pulse trains which each comprise pulse packets which each consist of a sequence of pulses whose pulse shape and / or polarity is configured individually. The invention further provides an apparatus for use in a method of stimulating a tissue through a magnetic field,

wherein a complex pulse sequence, consisting of individually confi ^¬ tured pulses with variable pulse shape is generated by a pulse generator means,

wherein the generated pulse sequence is applied to a stimulation coil with an adjustable repetition rate, which generates the magnetic field from ^¬

wherein a pulse capacitor of the pulse generator device is recharged by a charging circuit with the set Repetierrate.

In the following, possible embodiments of the magnetic stimulator according to the invention for stimulating a tissue by means of a magnetic field will be explained in more detail with reference to the attached figures.

1 shows a block diagram of a conventional magnetic stimulator according to the prior art; a block diagram illustrating a possible embodiment of a magnetic stimulator according to the invention for stimulating a tissue by a magnetic field; a further block diagram illustrating an embodiment of the magnetic stimulator according to the invention; a diagram for explaining a made by the controller system test in the magnetic stimulator according to the invention; a block diagram for illustrating an embodiment of a set in a pulse generator device of the magnetic stimulator according to the invention ^¬ set driver circuit;

Signal diagrams for explaining a zero-current detection, which is used in the driver circuit used in Figure 5. a circuit diagram illustrating an embodiment of a pulse generator means in which the stimulation coil is connected in a full bridge;

Fig. 8 diagrams for explaining the operation of the in

FIG. 7 shows a full bridge circuit for generating pulses from pulse segments; FIG. FIG. 9 is a signal diagram for explaining the driving of the full-bridge circuit having alternating polarities shown in FIG. 7; FIG. Fig. 10 is a signal diagram for explaining the driving of the full-bridge circuit shown in Fig. 7 with a single polarity;

FIG. 11 shows a signal diagram to illustrate a triggering of the full-bridge circuit with holding phases shown in FIG. 7; FIG.

Fig. 12 shows a possible implementation of a switched full-bridge circuit;

FIG. 13 is a signal diagram illustrating an exemplary asymmetric pulse shape; FIG.

14 is a block diagram illustrating an exemplary embodiment of a set up within the Pulsgenera ^¬ gate means of the magnetic stimulator charging circuit.

FIG. 15 shows a charging curve for explaining the mode of operation of the energy intermediate circuit used in FIG. 17 within the charging circuit; FIG.

FIG. 16 shows a signal diagram for illustrating the voltage curve on a pulse capacitor and for controlling charging switches of the charging control provided within the charging circuit shown in FIG. 14; FIG. FIG. 17 is a block diagram of a pulsed charging circuit used within the Pulsgenera ^¬ gate device of the present invention Magnetstimula- tors; FIG. 18 is a current waveform for explaining the operation of a particular embodiment of the clocked charging circuit shown in FIG. 17; FIG.

19 is a circuit diagram showing an embodiment of a power form correction circuit as a step-up converter;

Fig. 20 is a circuit diagram showing a Ausführungsva ^¬ riante of einge- in the clocked charging circuit translated charge controller,

Fig. 21 is a diagram showing a charging current of a

Pulse capacitor shown in Fig from ^¬ design variant 20 of the charge controller.

FIG. 22 is a diagram illustrating 17 can be inserted a further embodiment of the charge controller, in the getak ^¬ ended charging circuit shown in FIG.

FIG. 23 shows a diagram for illustrating the current flow, in the variant of a charge controller illustrated in FIG. 22; FIG. Fig. 24 is a circuit diagram showing another one

Embodiment variant of a charge controller, as it can be used in the clocked charging circuit of FIG. 17; a diagram illustrating a workflow for the configuration of pulse shapes of a complex pulse sequence used in the magnetic stimulator according to the invention;

Diagrams for illustrating realizable pulse variants, which may be contained in a complex pulse sequence of the magnetic stimulator according to the invention; a diagram illustrating a pulse packet within a complex pulse sequence, wherein the pulse packet from a predetermined number of pulses be available; a signal diagram for representing a plurality of Pulspa kete, each composed of individual pulses; a signal diagram for representing a single wave, as it may be contained within a complex pulse ^¬ frequency of the magnetic stimulator; a signal diagram for representing a Doppelwel le, as may be contained within a complex pulse sequence of the magnetic stimulator according to the invention; a diagram illustrating a complete complex pulse sequence with multiple pulse trains, each consisting of pulse packets, which in turn are composed of configurable pulses, how it can be delivered by the magnetic stimulator according to the invention to a stimulation coil;

Fig. 34 is a signal diagram illustrating a complex

 Pulse sequence with an evaluation pulse contained therein for explaining an embodiment variant of the magnetic stimulator according to the invention;

35 shows a diagram for explaining the operating sequence of a possible embodiment ^{variant of} the inventive magnetic stimulator;

Figure 36 is a diagram for explaining a variant of the magnetic stimulator used in the inventive user editor with a Stimulusdes ^¬ igner.

Fig. 37 is an illustration of the pulse packet assistant used in the user editor;

FIG. 38 is a diagram showing a pulse train assistant used in the user editor; FIG.

Fig. 39 is a diagram illustrating a stimulus designer employed by the user editor;

Fig. 40A is a diagram showing a pulse packet and pulse train assistant used in the user 40B editor;

FIG. 41 is a diagram illustrating a pulse selector used in a possible embodiment; FIG. Fig. 42 shows an example of a pulse composed by a user editor; Fig. 43 is a graph showing a normalized muscle potential as may be caused by the magnetic stimulator of the present invention as compared with a conventional magnetic stimulator; A diagram illustrating a normalized muscle potential such as may be caused by the novel magnetic stimulator for different current flow directions ^¬ Fig. 44; Figure 45 is another diagram of a normalized muscle potential, such as may be caused by the magnetic stimulator OF INVENTION ^¬ to the invention when using a double sine wave.

Diagrams for illustrating a motor Schwel le as a function of a current flow direction used in the magnetic stimulator according to the invention.

Fig. 2 shows an embodiment of a magnetic stimulator 1 according to the invention for stimulating a tissue by a

Magnetic field. The fabric can be, or ^¬ ganisches tissue of a patient P, for example, in particular Ge ^¬ brain tissue. The magnetic stimulator 1 has in the ^{dargestell ¬} th embodiment, a pulse generator 2 and a programmable controller 3. The pulse generator device 2 contains at least one pulse capacitor, which can be charged by a charging circuit for generating a pulsed pulse sequence with an adjustable repeating rate is. The control device 3 is a programmable control device which adjusts or controls the pulse generator device Z to generate a complex pulse sequence PS. This complex pulse sequence can have individually configurable pulses. The generated by the pulse generator means ^¬ 2 complex pulse sequence PS is delivered to a treatment coil or stimulation coil 4 via a line. 5 The line 5 may be a high-voltage or high-current line. The treatment or stimulation coil 4 is located in the vicinity of the tissue to be stimulated, for example the brain tissue ei ^¬ nes patient P, as indicated in Fig. 2. In the embodiment shown in Fig. 2, the programmable controller 3 of the magnetic stimulator 1 via a

Interface 6 connected to a computer 7.

A user editor for configuring a complex pulse sequence is preferably provided in the computer 7. The computer 7 can be a PC, a tablet computer or a laptop computer, whose user editor can be used to generate or configure the complex pulse sequence PS. In one possible embodiment variant, the user editor can be displayed via a graphical user interface GUI to a user who, for example, treats the patient P. In one possible embodiment, the user editor has a stimulus designer for configuring a pulse shape of individual pulses. In addition, the user editor employed may include a pulse packet assistant for configuring at least one pulse burst pulse packet. Furthermore, the user editor can also have a pulse train assistant for configuring at least one pulse train consisting of pulse packets. In this way it is possible for a user, one on the individual Needs of the patient P tuned complex pulse sequence PS to configure or program. There is the complex pulse sequence PS of pulse trains PZ, each comprising Pulspa ^¬ kete PP, which in turn consist of a sequence of powder-sen. The pulse shape of the pulses or individual pulses are preferably individually configurable in terms of their pulse shape and / or polarity using the user editor. In one possible embodiment, the pulse sequence PS configured by means of the user editor is transmitted via the interface 6 to the programmable control device 3 of the magnetic stimulator 1 and can be stored in a memory unit 8 of the magnetic stimulator 1. The memory 8 may be, for example, an EEPROM memory. The interface 6 is suitable for transmitting complex pulse patterns. For example, the interface 6 may be a USB or Ethernet interface.

In the illustrated in Fig. 2, the programmable controller 3 of the magnetic stimulator 1 via a separate circuit 9 is attached to a lead electrode 10 ^¬ closed. The Ableitelektrode 10 is for example an adhesive electrode for deriving an EMG signal. The Ableit ^¬ electrode 10 is connected via a line 11 to the circuit 9, which is provided for amplifying, digitizing and recording of muscle signals. The circuit 9 can on the one hand via a line 12, a trigger signal and on the other hand via a line 13, a measurement signal to the pro ^¬ programmable controller 3 of the magnetic stimulator 1 from ^¬ . By means of the trigger signal, the magnetic stimulator 1 can signal the pulse delivery to a recording device. To the delegation ^¬ supply the trigger signal via the line 12 can also be bidi ^¬ directionally. Via the line 13, a measured signal can be fed back to the magnetic stimulator 1 in order to For example, adjust stimulation parameters of the delivered to the patient P stimulation signal. This stimulation ^¬ parameters include for example the intensity or Fre ^acid sequence of the signal. In one possible embodiment, the signal path 13 is deactivated. In this case, the signal path 13 is not used because a self-regulating, fast pacing system in certain cases poses a medical risk, such as an epileptic seizure in which patient P may cause. In other Fäl- len of Rückführsignalweg or feedback signal channel acti is fourth ^¬ to use the feedback for automated determination of parameters, in particular a motor threshold. For example, to determine the ^motor threshold approximately every 10 seconds, a stimulation pulse with a certain intensity is delivered to the patient P and the muscle response is evaluated. By using a maximum Like-lihood method, the intensity as long varies ^¬ to until a certain fraction of the measured muscle responses within a certain voltage range (for example, 15 generate 20 pulses muscle response potential of> 50 μν at an intensity of 65% of the maximum Stimulator outputs). This intensity is then the motor threshold of the patient P. In this variant, the determination of the motor threshold can automatically executed advertising to, whereby the user convenience is increased for the user and at the same time, the determination of the motor threshold of Pa ^¬ tienten P faster can ,

Fig. 3 shows a block diagram illustrating circuitry of technical details within the inventive magnetic stimulators 1. In the in Fig. 3 shown execution ^¬ for the pulse generating means 2 includes a La ^¬ deschaltung 2a, a resonant circuit 2b with pulse switch is connected to the stimulation electrode 4 or treatment, and 2c, a coil supervision circuit also connected to the stimulation electrode or treatmen ^¬ lung. 4 The programmable controller 3 and the various units or assemblies of the pulse generator device 2 can exchange device-internal control signals, for example via an internal CAN bus. The pulse generator device 2 includes a charging circuit 2a, which is provided for reloading the pulse capacitor with adjustable repeating rate. The pulse capacitor C _PULS preferably forms part of a resonant circuit in which the stimulation or treatment coil 4 is also located. The charging circuit 2a is preferably connected via a network connection to a power supply network. The programmable controller 3 may include a plurality of interfaces or interfaces, in particular an interface 6 for connection to the computer 7 and a trigger input or output 12 for connection to the signal processing circuit 9 and an interface 13 for receiving a Rückführsig ^¬ nals of the Ableitelektrode 10th ., shown in Fig. 3 programmable controller 3, serves essentially for From ^¬ sequence control of the complex pulsing protocols and for monitoring critical parameters of the magnetic stimulator 1 as well as for communication with the user or users. In one possible embodiment, the programmable controller 3 has its own graphical user interface GUI, so that the programming of the complex pulse sequence PS without connection of an external computer 7 is possible.

In one possible embodiment variant, the programmable control device 3 causes the pulse generator device 2 to deliver the pulse sequence PS to the stimulation coil 4 only after a system check of parameters of the magnetic stimulator 1 has been successfully completed. Fig. 4 shows a Flowchart illustrating a variant of a performed by the programmable controller 3 system test. In the case of a possible embodiment variant, various parameters are queried during the system test, which concern the coil monitoring, the resonant circuit, the charging circuit and / or a user communication. For example, can be checked whether a treatment or Stimulati ^¬ onsspule 4 is connected to the magnetic stimulator 1 and inserted reasonable was tested for the first coil supervision. Furthermore, it is monitored how high the coil temperature ^¬ the stimulation coil 4. Furthermore, it can be checked whether all modules respond to commands of the programmable controller 3 or respond. The coil monitoring circuit 2c of the pulse generator device 2 shown in FIG. 3 can, in one possible embodiment variant, monitor whether a stimulation coil 4 is actually connected to the magnetic stimulator 1. In one possible embodiment, the detection as to whether a stimulation coil 4 is present or not can take place by means of a shorting bar installed in a coil plug, coding resistor or by RFID tags or by an impedance measurement on the stimulation coil 4. In a further possible embodiment variant, the coil monitoring circuit 2c additionally has sensors for monitoring operating parameters of the stimulation coil 4. In one possible embodiment, the coil monitoring circuit 2c has temperature sensors for monitoring an operating temperature T of the treatment coil or stimulation coil 4. In this case, in particular checked whether the surface temperature of the stimulants lationsspule 4, with which the patient P comes in contact, egg ^¬ ne temperature, for example 40 ° C exceeds. The coil monitoring circuit 2c evaluates the temperature values supplied by the temperature sensors. In one possible Embodiment, the coil monitoring circuit 2c two temperature sensors and compares their two values with each other. The two measured temperatures differ significantly from each other and the temperature, for example above 40 ° C, a wide ^¬ re pulse discharge is blocked off by pulse generating means 2, respectively, and, if necessary, an error is reported via a user interface to the user by the programmable controller. 3 Furthermore, the programmable control device 3 can block or deactivate the delivery of pulses if no stimulation coil 4 is connected to the magnetic stimulator 1 or inserted therein. As a result, for example, the unwanted formation of an arc can be prevented. In a possible embodiment variant, the monitoring of the sensors, in particular of the temperature sensors, can be performed by at least one microprocessor. In this case, the microprocessor can be constructed in a variant redundant with mutual verification. Alternatively, a redundant supervisory channel may be implemented by discrete hardware.

In the system test shown in FIG. 4, further parameters with respect to the resonant circuit with pulse switch can be checked. For example, it can be determined how high the operating temperature is at a circuit breaker provided therein. Furthermore, it can be checked whether the assemblies affected respond to commands of the programmable controller 3. In addition, it can be checked, for example, whether all necessary auxiliary voltages are present.

Furthermore, the system test can check parameters of the charging circuit 2a. For example, it is checked whether there are voltage ^¬ asymmetries on an intermediate circuit of the charging circuit 2a. Furthermore, voltage asymmetries on the pulse capacitor C _PULS can be checked. Furthermore, it can be checked whether all voltages, for example on the DC link or pulse capacitor, are within a permissible voltage range. Furthermore, it is checked, for example, whether the temperature at a charge controller of the charging circuit 2a is within a valid range.

Furthermore, the system check shown in FIG. 4 can check parameters of the user communication. For example, it is checked whether a user has selected or transmitted a valid pulse pattern or a valid complex pulse sequence PS. Furthermore, it can be checked whether the user or user wants to cancel the current delivery of the pulse sequence PS or not. If one or more of the checked pulse parameters indicates that a critical condition exists, or the user wishes to interrupt the pulse delivery, the pulse output by the pulse generator device 2 is automatically prevented or blocked by the programmable control device 3.

In one possible embodiment of the programmable controller 3, this has one or more microprocessors. These microprocessors can to the other modules of the system on a real-time fault-tolerant and fault detecting bus, preferably a CAN bus, being included be ^¬ and about communicate with the modules.

In one possible embodiment, the interface is formed into the user or user through a standardized interface by means of certain standardized data transmission protocols ^¬, preferably USB or Ethernet. The programmable control ^device 3 of the magnetic stimulator 1 can be connected to a computer 7, for example via this interface. as a PC, laptop or tablet computer, or to a mobile device, in particular a smartphone or the like, are connected. Furthermore, the programmable controller 3 can be connected via corresponding interfaces to measuring and exchange measuring devices and have a trigger input and a trigger output. In a possible embodiment variant, the programmable control device 3 is connected to display elements or display devices of the magnetic stimulator 1.

As shown in FIG. 3, the pulse generator device 2 of the magnetic stimulator 1 has a resonant circuit with a pulse switch 2c. Here are different variants. In a possible embodiment, the resonant circuit is implemented with pulse switch 2c with a single circuit breaker. In a further possible embodiment, the resonant circuit with pulse switch 2c is constructed from a full bridge. In a further embodiment, the resonant circuit with pulse switch 2c consists of a full bridge with switched pulse capacities.

The first embodiment of the resonant circuit with pulse ^¬ switch 2c with a circuit breaker allows only the delivery of biphasic (sinusoidal) pulse shapes / stimuli. In contrast, the embodiment in which the resonant circuit is built with pulse switch as a full bridge on ^¬, at least four power switches but has since ^¬ for the benefit of a largely free design of the respective pulse shape required. With this embodiment variant, the complex pulse sequence can be completely parameterized by the user. The resonant circuit with pulse switch 2c has at least one power switch, which is connected to a controllable by the programmable controller 3 driver circuit. In a possible embodiment, this driver circuit or drive circuit for the power switch has a maximum switching frequency. For the circuit breaker, an IGBT circuit breaker is preferably used. The maximum switching frequency of the drive or driver circuit is 100 kHz in one possible embodiment. Fig. 5 shows a block diagram of an embodiment of a controllable Moegli ^¬ chen driver circuit TS, which is constructed for a power switch SW. The circuit breaker is preferably an IGBT circuit breaker. This IGBT power switch is located in the resonant circuit 4 between the pulse capacitor C _PLUS and the stimulation coil 4, as shown in Fig. 5. In the embodiment variant shown in FIG. 5, the driver circuit TS includes a microprocessor MP which is connected to the programmable controller 3 via a CAN bus. The driver circuit TS shown in FIG. 5 has a current zero crossing detection for the detection of an inductance L of the treatment or stimulation coil 4. With the current zero crossing detection, the switching behavior of the driver can be adapted to the inductance L of the stimulation coil 4, as shown in FIG. 6A-6E. Figure 6B -. 6E show examples of the timing of the current zero passage ^¬ at different inductances L and particularly in the case of short circuit, ie with shorted turn with existing residual inductance. 6A shows the resonant circuit connected to the charging circuit 2a and the power switch SW contained therein. Fig. 6B shows the current zero crossing with appropriate inductance. 6C shows the course when the inductance of the stimulation coil 4 is too large, and FIG. 6D shows the case with too small inductance of Stimuli ^¬ tion coil 4. Fig. 6E finally shows the short circuit case. In one possible embodiment, the Stromnull- done by gang recognition in the driver circuit TS on the measure- ment of a voltage drop across the respective power ^¬ switch SW. This offers the particular advantage, in comparison to a current measurement on the conductor, that the voltage which actually also bears against the protective component and not a current which is present in the conductor, ie in front of the IGBT module, is measured. In addition, in this procedure, the voltage change occurs only when a caused by a reverse recovery effect short-term reverse recovery current has subsided after the current zero crossing.

As shown in Fig. 5, the microprocessor MP of the driver circuit TS, a sensorially detected temperature T of the resonant circuit, in particular the stimulation coil, auswer ^¬ th. The driver circuit TS shown in Fig. 5 may include bi- polar driver wherein an outer voltage, the

Microprocessor MP can be returned, as shown in Fig. 5. An asymmetrical gate control +18 V / - 12 V can be provided for safe switching on and off. Furthermore, it is possible that auxiliary voltages are monitored by the microprocessor MP. The microprocessor MP, as shown in Fig. 5, a pulse command to an AND gate, which can receive a redundancy signal. In one possible embodiment, the turn-on time is between 1 and 2 microseconds in order to reduce turn-on losses. Furthermore, in a possible embodiment, the

Off time is 8 microseconds, which together with a discrete hardware circuit leads to a minimization of circuit overvoltages. In a possible embodiment, only a single power switch SW, in particular IGBT switch is provided to the resonant circuit. In this embodiment, the pulse shape that can be used within a complex pulse sequence is exclusively sinusoidal. The advantage of this embodiment is the low implementation effort. In a preferred alternative embodiment, the resonant circuit with pulse switch is implemented within a full bridge. FIG. 7 shows a ^circuit diagram for illustrating an exemplary embodiment of a full-bridge circuit for flexible pulse forms. In this embodiment, the stimulation coil 4 is connected in a full bridge with four power switches Ql, Q2, Q3, Q4 for generating pulses whose pulse shape can be composed of pulse segments. The voltage across the pulse capacitor C _PULS has the pulse is determined by the charging circuit 2a. The various circuit breakers Ql to Q4 can be controlled via an associated IGBT driver. The capacitors C 1, C 2 provided in the circuit according to FIG. 7 serve for voltage balancing. Furthermore, the full bridge circuit shown in Fig. 7 may include a so-called snubber circuit SN, which is provided for lowering voltage spikes, which may occur when switching off an inductance L. The pulse capacitor C _PULS is used for energy storage. The snubber circuit SN includes some capacitors C3 to CIO which are connected to the stimulation coil 4 via resistors R1, R2. For example, the snubber capacitors have a capacitance between 100 to 300 nF. The snubber resistors Rl, R2 may, for example, a resistance value of 1 to 10 ohms aufwei ^¬ sen. Free wheel diodes D1 to D4 may be provided in parallel with the IGBT circuit breakers Q1 to Q4, as in FIG Fig. 7 shown. The Symmetrisierungskondensatoren Cl, C2 may each have a capacity of 0.1 to 1 microfarad in a possible embodiment. The pulse capacitor C _PULSS preferably has a relatively high storage capacity of more than 20 pF, for example 66 pF. The capacity of the pulse capacitor C _PULS can be a few mF.

FIG. 8 shows diagrams for illustrating a current flow in the full-bridge circuit shown in FIG. 7. Since the current flow through the LC resonant circuit, which includes the pulse capacitor C _PULS and the stimulation coil 4, comes about, the current flow has a sinusoidal course. The amplitude of the oscillation is determined by the charging voltage of the pulse capacitor C _PULS . The frequency of the oscillation results from the capacitance C _{PLUS of} the capacitor and the

Inductance L of the coil 4. As a segment of a sinusoidal oscillation can be realized with the full bridge circuit shown in FIG. 7 also holding phases, ie it can be almost any number of different pulse shapes can be realized. For this purpose, the coil 4 is short-circuited in phases during the power line, as shown in Fig. 8A. In this case, the energy is retained within the coil 4. In this case, an attenuation is taken into account, which can occur both during the sinusoidal oscillations and during the holding phases. The damping coil by the ohmic losses of the stimulation ^¬ 4 of the pulse capacitor C _PL us and the electrical Lei ^¬ obligations caused. Furthermore, the current profile is attenuated by time losses at the circuit breakers Qi. . In the embodiment shown in Fig 7 embodiment, the performance-switch Qi are implemented by IGBTs, each of which free-wheeling diodes Dl ^¬ - D4aufweisen. Therefore, it is sufficient in the embodiment of the full-bridge circuit shown in FIG. 7, while the holding phases only a power switch Qi to keep closed. It must be closed, for example, the holding ^¬ phase on a positive level, only the power switch Q, the diode D4 to the power switch ^¬ Q4 switch Q4 for the required current direction will close automatically.

When using the full-bridge circuit shown in FIG. 7, there are three possible segment types with which a single pulse can be set up or configured, namely a rising section (sinusoidal with a time constant T = L × C _PULS ), a constant section and a sloping section (sinusoidal with a time constant T = L

x Cp _UL s), whereby ohmic losses are neglected. These three segments can be strung together in almost any length and in any combination. As a result, arbitrary pulse shapes can be generated within wide limits. In this case, switching losses and a minimum duty cycle are taken into account, since the power switch Q can not be switched with any frequency.

Fig. 8A shows various current flow phases through the full bridge circuit shown in Fig. 7. Fig. 8B shows associated segments for a generated single pulse.

Exemplary pulse shapes with a representation of the associated switch positions are shown in FIGS. 9, 10, 11. Thus, FIG. 9 shows the control of the full bridge scarf ^¬ tung with alternating polarities. 10 shows the activation of the full-bridge circuit in a single polarity. 11 shows the activation of the full-bridge circuit with holding phases. FIG. 12 shows an extension of the full-bridge circuit to at least two pulse capacitors. For this purpose, several La ^¬ deschaltungen can be provided. An advantage with in

12 is that the various pulse capacitors can be charged to different voltage levels. This allows an even higher repetition rate than 1 kHz. The higher repetition rates can be achieved by providing the necessary pulse energy alternately from the different pulse capacities. A further advantage of the ^embodiment variant consists in a possible use of different time constants which, in contrast to the simple full bridge circuit according to FIG. 7, opens up the possibility of configuring or forming strongly asymmetrical pulse shapes, as illustrated in FIG. 13. The use of asymmetric pulse shapes within the complex pulse sequence PS potentially allows the stimulation of other brain areas in the treated patient P. FIG. 13 shows by way of example a strongly asymmetric pulse shape with two time constants and T ₂ .

The pulse generator device 2 used in the magnet st imulator 1 contains a charging circuit 2a which is provided for recharging the pulse capacitor C _PL us with a high adjustable repecification rate. In one possible embodiment, the recharging of the energy lost during the pulse delivery of the pulse capacitor C _{PULS takes place,} for example, within a period of 1 ms. In this variant, be ^¬ carries the maximum repetition rate 1 kHz. In one possible embodiment, the charging current for charging the pulse capacity is about 100 A. In one possible embodiment, the charging circuit 2a used in the pulse generator device 2 is a linear charging circuit. In a further alternative embodiment, the charging circuit used in the pulse generator device 2 is a clocked charging circuit.

Fig. 14 shows a block diagram for a possible exporting ^¬ approximate shape of a linear charging circuit 2a, as it can be used within a pulse generator 2 of the magnetic stimulator. 1 The charging circuit 2a serves to charge the pulse capacitor to a specific voltage level U _FULL and to recharge the lost energy after pulse delivery within the short time, for example, a maximum of 1 ms. The linear charging circuit 2a shown in FIG. 14 has a power supply NT for connection to a power supply network, a

Energy intermediate circuit EZK for temporary storage of the electrical power supplied by the power supply NT and a charge controller LR, which is connected to the resonant circuit of the Pulsgenera ^¬ gate device 2. The used power supply PS may be a standard power supply or a trans ^¬ formator with rectifier. The output voltage U _{PS of} the power supply NT may be, for example, in the order of 2000 to 4000 V. The illustrated in Fig. 4 Power ^¬ some NT can be run either as a single-phase or three-phase power supply as NT in different versions. Due to the low duty cycle for the pulse output conventional single-phase power supplies are preferably incorporated ^¬ continues to provide the necessary pulse power available to stel ^¬ len.

For the linear charging circuit 2a according to FIG. 14, an energy intermediate circuit EZK is provided on the DC side of the power supply. This power link EZK is used for buffering and storage of the electrical energy supplied by the power supply unit NT. The intermediate circuit voltage in the energy intermediate circuit EZK is preferably chosen to be greater than ei ^¬ ne maximum reference voltage UsoLLmax on the pulse capacitor C _PUL S of the resonant circuit to exploit the transconductance of an RC charging curve, as shown in Fig. 15, and thus a fast energy recharge to enable in the power link EZK. A provided in the intermediate circuit power EZK capacitor has a capacitance C _zw, which is preferably substantially larger than the pulse capacitor C _PULSE of the Pulskon ^¬ densators so that the largest possible energy supply can be provided ^¬.

The linear charging circuit 2a shown in FIG. 14 includes a charge regulator LR which is connected to the power intermediate circuit EZK. The charge controller LR charges the pulse capacitor of the pulse capacitor to a setpoint voltage U _SOLL . For this purpose, charging switch Sl to S4 are of the charge controller LR depending on the existing at the pulse capacitor actual voltage U _c actuated. The charging switches S1 to S4 may preferably be formed as IGBT switches due to the high voltage and fast switching phases. The actual voltage at the pulse capacitor is detected and processed by a microprocessor MP of the charge controller LR. The microprocessor MP of the charge controller LR then controls the load switches Sl to S4.

In addition, the temperatures at the charge and discharge resistors Rl to R4 can be monitored by the microprocessor MP. The switch S5 in combination with the resistor R5 is provided for an emergency discharge of the pulse capacitor in a fault. The switch S5 is preferably designed as a high voltage relay. This high voltage relay can be switched via the microprocessor MP. In a possible embodiment, the high voltage relay for the sake of redundancy of a discrete hardware circuit (not shown) are switched.

The microprocessor MP of the charge control LR within the linear charging circuit 2a may in one possible embodiment be connected to the device control or the programmable control device 3 via a CAN bus. In one possible embodiment, the microprocessor MP is used as a redundant component. In this embodiment, two microprocessors are installed, which are interconnected in the same way. These two microprocessors mutually check their measurement and control results. Turns out at ^¬ play as one of the two microprocessors or enter the two microprocessors conflicting results, so in a possible variant of a Notent ^¬ charge using the switch S5 and the resistor R5 can he follow ^¬. If no redundant microprocessors installed in an alternative embodiment, it is preferential ^¬, a further redundancy circuit for monitoring the voltage implemented. When an error occurs, in particular when an overvoltage occurs, this test circuit or test instance then switches off the high voltage with the aid of the switch S5 and the resistor R5. This redundancy ^¬ circuit is provided in particular when using the Magnetst imulator 1 as a medical device.

16 shows signal diagrams for illustrating the behavior of the charging switches S1 to S4 within the charge regulator LR of the linear charging circuit 2a, as shown in FIG. In the embodiment shown in Fig. 16, the control of the charging switches Sl to S4 via bipolar driver stages takes place directly from a microprocessor MP of the charge control LR. Fig. 16 shows the voltage waveform U _c at the Pulse capacitor and necessary control signals for the La ^¬ deschalter Sl to S4 for different scenarios.

The charge circuit 2a inserted inside the pulse generator device 2 of the magnetic stimulator 1 for recharging the

 Pulse capacitor with an adjustable repeating rate may be a clocked charging circuit in another embodiment. Fig. 17 is a block diagram showing an embodiment of a clocked charging circuit 2a. The clocked charging circuit 2a has a power supply unit NT for connection to a power supply network, a first DC / DC switching regulator for continuous operation, an energy intermediate circuit EZK for buffering the electrical energy supplied by the first DC / DC switching regulator, and a second one DC / DC switching regulator for pulse operation, which is connected to the circuit of the pulse generator device 2, as shown in Fig. 17. The power supply includes a diode full bridge and an input filter. The first DC / DC switching regulator connected to the power supply unit is designed for continuous operation, for example for one

2000 W continuous power. The first DC / DC switching regulator charges an intermediate circuit capacitor C _s of an energy intermediate circuit EZK continuously on a predetermined voltage, for example 400 V. The energy intermediate circuit EZK is preferably designed DER art that the energy stored in the intermediate ^¬ circuit capacitor is large compared to the maximum storable energy in the pulse capacitor C _{PULS of} the resonant circuit is. The second DC / DC switching regulator of the clocked charging circuit 2a shown in FIG. 17 is for a pulse operation for the transmission of large amounts of energy, for example, up to

5000 W, designed. In this case, preferably the duty cycle is ^suitably dimensioned. The second DC / DC switching regulator charges the pulse capacitor C _PULS during pacing pauses. Of the second DC / DC switching regulator is not driven when the oscillation circuit switch SW, as shown in Fig. 17, is closed and a pulse is emitted. The second

DC / DC switching regulator acts directly on the pulse capacitor C _{PULS of} the resonant circuit and must therefore drive only a ka ^¬ pazitive load. This means that high voltage ripples due to the pulsed charging process are of no importance, since the charging voltage at the pulse capacitor C _{PULS is} only used for pulse delivery when the second DC / DC switching regulator is no longer active.

In one possible embodiment, a power form correction PFC takes place at the first DC / DC switching regulator of the clocked charging circuit 2a. This circuit stage is used to perform a normative prescribed power shape correction from a certain nominal power. With such a power shape correction, one can achieve that the current consumption from the power supply network is as sinusoidal as possible. FIG. 18 shows a possible current flow at the converter input in comparison to a purely sinusoidal current consumption. The

Operation of the power form correction consists of controlling the absorbed current as a function of the sinusoidal voltage measured at the input (operating mode CCM = Continuous Conduction Mode). The illustrated in Fig. 18, solid line is thus a sinusoidal Idealzu ^¬ stood on. The dashed line shows the other power line with the PFC again and shows switching time ^¬ points of the converter (it represents an approximation to the Ideal ^¬ state).

One possible implementation of a power form correction (PFC) circuit as a boost converter is shown in FIG. If the provided switch Sl closed, builds a coil current through the coil L on. If the switch is then opened again, the current flows via the diode D into the DC link capacitor C _s , wherein the coil current decreases again. When a lower threshold value is reached, the switch S1 is closed again and the coil current rises again. A particular advantage of the Darge ^¬ presented in Fig. 19 embodiment is the possibility that on ^¬ due to the low voltages at the intermediate circuit capacitor (for example, 400 V) may be formed by the switches Sl to as MOSFET excluded. Alternatively, the switch Sl may also be implemented as an IGBT power switch.

For the charge controller within the clocked charging circuit 2a shown in Fig. 17, there are various embodiments variants. In a possible embodiment, the second DC / DC switching regulator is implemented as a push-pull flux converter, as shown in FIG. In this exporting ^¬ approximately variant of the pulse capacitor C _PULSE can only be loaded ^¬ to. A discharge of the pulse capacitor via a further switch and a loading ladder resistance, similar to the linear charging circuit. In this embodiment, the pulse capacitor C _PULS can therefore be charged only with a Polari ^¬ ity and a polarity reversal is not readily possible. Fig. 21 shows a current flow through the Pulskonden- sator C _PULSE · In the illustrated embodiment, the flow of current I no gaps, ie there is a continu ously flowing ^¬ charging current. By controlling the transformer with an H-bridge, it is alternately loaded in both current directions.

In a further embodiment variant, the charge controller LR of the clocked charging circuit 2a shown in FIG. 17 can be designed as a flyback converter for charging the pulse capacitor C _PULS be. FIG. 22 shows a circuit diagram of a variant in which the charge regulator LR is realized as a flyback converter. This reduces the circuit complexity relative to the push-pull type flux converter shown in FIG. When in Fig. 22 variant shown LR of the charge controller of the pulse capacitor C _PULSE is loaded only when power is removed from the over ^¬ tragungstransformator, that is, the charging current has gaps, as shown in Fig. 23. If the ^switch S1 of the charge controller LR shown in FIG. 2 is closed, the current through the transformer increases, energy being transported. In contrast, if the switch Sl of ^¬ fen, energy flows from the transformer into the pulse capacitor, the current flow in the transformer drops again until the switch Sl is closed again. Nachtei- lig is the intermittent operation of the charging current, with the same energy transfer amount a higher Stromommaxi ^¬ mum than in the push-pull flow converter, as shown in Fig. 20, is necessary. A further disadvantage of the charge controller LR shown in FIG. 22 is that the pulse capacitor C _PULS can only be charged with one polarity, ie, a polarity reversal is not readily possible.

In a further embodiment of the charge controller within ^¬ half of the clocked charging circuit shown in Fig. 17 this is as a flyback converter for charging and discharging the

Pulse capacitor executed. In this embodiment, the flyback converter is extended by a further switch, as shown in Fig. 24. In this way, the circuit topology can be used both for charging and for discharging the pulse capacitor C _PULS .

In the case of the embodiment variants of the charge controller LR shown above, in each case the measuring devices for the tenen voltages and the associated microprocessor for controlling the switch for clarity not shown. As long as the switch S7 is in the position shown in Fig. 24 embodiment held open and switch Sl is ge ^¬ clocks, the transducer as the previously beschrie ^¬ bene embodiment behaves according to Fig. 22. To the contrary, the switch Sl kept open and the switch Initially actuated in a clocked manner, energy is first transferred from the pulse capacitor C _PULS into the transformer (switch S7 closed) and then transferred again from the transformer to the intermediate circuit capacitor C _s (switch S7 closed). In this realization, the effects of the voltage level of the intermediate circuit capacitor C _s and thus also of the first DC / DC switching regulator are taken into account. For example, ver ^¬ searches the first DC / DC switching the voltage at the intermediate circuit capacitor C hold, however, it may be tolerant to 500 V charging voltage _s at a voltage of 400 V. This voltage can be achieved if the intermediate circuit capacitor C _{s has} a voltage level of 400 V and, in addition, the pulse capacitor is completely discharged with respect to the intermediate circuit capacitor C _s . In the embodiment variant shown in FIG. 24, the switch S7 can not be filled out as a MOSFET due to the relatively high voltage levels. Therefore, the switch S7 is preferably executed in this embodiment as an IGBT switch. An advantage of the circuit topology illustrated in FIG. 24 is that energy recovery is achieved through the active discharge process.

The charging circuit 2a of the pulse generator device 2 within the magnetic stimulator 1 can be designed as a linear charging circuit. forms his or as a clocked charging circuit. For example, Fig. 14 shows an embodiment with a linear charging circuit. In contrast, Fig. 17 shows a variant with a clocked charging circuit. The linear charging circuit required in relation to the clocked charging circuit a large, high voltage suitable DC link capacitors tor with a capacitor voltage, for example more than 2000 V. The resistors through which the energy is transferred from the interim ^¬ intermediate circuit in the pulse capacitor C _PULSE, leadership ren next the pulse losses during the pulse delivery to the

Stimulation coil 4 to additional losses, which may be associated with a strong increase in temperature. In contrast, stores a clocked charging circuit, the intermediate circuit energy at a relatively low voltage level, for example, 400 V. The necessary high voltage for pulse delivery occurs only on the pulse capacitor itself or only at an output of the switching power supply. The losses within the ge ^¬ clocked charging circuit are therefore lower than when using a linear charging circuit. For this reason, the clocked charging circuit can be much more compact than the linear charging circuit

Charging circuit are constructed. In addition, the clocked La ^¬ circuit, which is shown for example in Fig. 17, a higher efficiency than the linear charging circuit. Therefore, in a preferred embodiment of the magnetic stimulator 1 according to the invention, a clocked charging circuit is used as charging circuit 2a of the pulse generator device 2.

In a preferred embodiment of the magnetic stimulator 1 according to the invention, the programmable control device 3 of the magnetic stimulator 1 can be connected via an interface 6 to a computer 7, on which a user editor for configuring the pulse sequence PS is provided. In this groove The editor is preferably a graphical editor that can be executed, for example, by the computer and can be displayed to the user via a graphical user interface (GUI) of the computer. When the user is, for example, a user who is treating any Pa ^¬ tienten P. In another possible embodiment, the user editor is executed on a computer (embedded PC) installed in the magnetic stimulator 1. In this embodiment variant, the magnetic stimulator 1 has its own graphical user interface (GUI).

Fig. 25 shows an example of a workflow for configura ^¬ tion or parameterization of a pulse with a particular pulse shape. In one possible embodiment, the pulse shape is first created using a special application Pulse desig ^¬ ner. This generated pulse can then be exported to a stimulator format. Then it is transmitted directly to the magnetic stimulator 1 via an interface. For the execution of an experiment or a session or session, the pulse can be further processed. For this, the pulse can be loaded with a Pulse Intensity application. This makes it possible einzu the desired pulse intensity ^¬ provide or generate a series of pulses. Furthermore, it is possible for the order of the pulses to be randomized via a special application of randomizers for the respective session. After creating the pulses, these can be charged, for example, on a USB stick and copied via a USB interface in the magnetic stimulator 1 who ^¬ . The generated pulses can also be copied into the magnetic stimulator 1 via another communication method. The thus created pulse with the special pulse ^¬ form and / or pulse polarity can in a possible execution variant are stored within a memory of the magnetic stimulator 1 for further use.

Fig. 26 is a diagram showing a stimulus consisting of a single wave (Fig. 26A) or a double wave (Fig. 26B). The stimulus shown consists of a single, a double or a multiple sinusoidal oscillation of the current through the Stimulationssspu ^¬ le 4. The stimulation pulse has an intensity Io and can at a defined time t by the user or user or according to the formed complex pulse log ^¬ be solved. The polarity of the stimulus or pulse can preferably be changed, ie the first sinusoidal oscillation is reflected around the time axis. FIG. 26 shows the representation of a stimulus or pulse for a positive single and double oscillation. The stimulus can be symbolically symbolized by a rectangle, as indicated in FIG. 26. Fig. 27 shows double pulses (paired pulses). Double pulses are two direct successive stimuli or pulses with the same or different amplitudes.

FIG. 27 shows the schematic representation of a double pulse with the associated current-time profile through the stimulation coil 4. The time interval between the two stimuli or pulses is denoted by t _PP and the intensity difference by ΔΙ. FIG. 27 shows the two most frequently used double pulse variants within a complex pulse train PS. In a possible variant embodiment, an evaluation pulse EP by such double pulse is gebil ^¬ det. Interstimulus interval is the time interval tisi between stimuli of equal intensity I. The pulse sequence or the pulse protocol PS represents a temporal serial arrangement of different stimuli or pulses, packets / bursts and double pulses with a defined property, which is automatically processed or dispensed. The pulse shape or stimulus shape is the waveform of the current time course through the stimulation or treatment coil. In the case of a biphasic stimulation of the patient P, these are, for example, single, double and multiple waves.

FIG. 29 shows the structure of a pulse packet PP within a pulse train PZ of a complex pulse sequence PS. A pulse packet or pulse burst PP denotes a container of n stimuli or pulses with an interstimulus interval t _IS i. Within a pulse packet or pulse burst PP, the intensity I, the polarity and the interstimulus interval of all pulses or stimuli are kept the same. A special case with n = 4 Stimu ^¬ li is called Quadropulsstimulation.

Fig. 30 is a diagram for explaining a packet interval and interburst interval, respectively. The package or Interburst- interval ti _B i is the time interval between two Pulspa ^¬ ketene or pulse bursts PP. The two consecutive pulse packets PP are not always identical.

Fig. 31 is a diagram showing a single wave. The single wave represents the simplest stimulus shape or pulse shape of the biphasic stimulation. The single wave consists of exactly one single sinusoidal oscillation with a predetermined period T, as shown in FIG. Fig. 32 shows a diagram of a double wave. The double wave consists of two sine waves, as shown in Fig. 32. So it is possible to string together as many sinusoids as you like. Due to a system-related attenuation of the device, however, the amplitude decreases exponentially, whereby a practical benefit of more than two oscillations only rarely exists.

33 shows, by way of example, a complex pulse sequence PS with a plurality of pulse trains PZ, each consisting of pulse packets PP, which in turn consist of a sequence of pulses. The pulse train PZ denotes a container of n different pulse packets or pulse bursts PP and forms a topmost nest level of a complex pulse sequence PS or a complex pulse protocol, as shown in FIG. 33. Different different pulse trains PZ can be strung together in succession. The time interval between two Pulstrains or pulse trains PZ is referred to as Intertrainintervall t _ITI .

The repetition rate indicates the number of stimuli or pulses per time. While conventional stimulators usually reach a repetition rate of 100 Hz, it is possible with the imulators 1 Pulsge ^¬ neratoreinrichtung 2 of Magnetst invention provide a repetition rate of up to 1 kHz and more einzu ^¬.

A basic protocol of a complex pulse sequence PS consists of pulse packets PP and the individual pulses or stimuli contained therein. The parameterization of a basic protocol can play specify the interstimulus interval tisi or the pulse form, or the proportion of pulses per pulse packet and the packet PP ^¬ interval TiBi at ^¬. Fig. 34 shows a protocol variant or a complex pulse sequence with a ^¬ contained therein Evaluation pulse EP. This evaluation pulse EP is provided between two pulse packets PP and may, for example, be designed as a double pulse. As a rule, a trigger signal is triggered by the magnetic stimulator 1 for this evaluation pulse EP in order to start, for example, an EMG amplifier for measuring a motor muscle response. In addition to the parameterisation sierungsmöglichkeiten a basic protocol, the following parameters may be used in the set in Fig protocol variant illustrated. 34: namely, the pulse intensity of the Evaluati ^¬ onspulses (0 to 100%), a pulse intensity difference ΔΙ between the two pulses of the double pulse which the Eva luationspuls EP forms (eg ΔΙ = +/- 20%). A distance from the last pulse packet t _EV (for example, 100 ms) and a distance to the next pulse packet t _DELAY (for example likewise min ^¬ least 100 ms). In one possible embodiment or protocol variant, the polarity of the individual pulses, or stimuli Zvi ^¬ rule can the different pulse packets PP of the complex pulse sequence PS to be replaced. For example, if the pulses of the first pulse packet PP are positive pulses, then the polarities of the pulses within the subsequent pulse packet PP may be negative. A polarity change of the pulses within a pulse packet PP is usually not provided.

In one possible embodiment variant of the magnetic stimulator 1 according to the invention, an I-wave latency is determined. The I-wave latency time varies from individual to individual or patient to patient, and may range from 1 ms to 2 ms for the fundamental. All other I- Wave latencies are integer multiples of this base latency. In one possible embodiment, the I-wave latency of the patient P is determined by the delivery of double pulses (pair pulse stimulation) with different Interstimulu- sintervallen by measuring a motor muscle response. Here, the interstimulus interval is adjusted as long kon ^¬ continuously until a maximum motor Mus ^¬ kelantwort is measured. This Inter stimulus interval ent ^¬ says the I-wave latency time of the patient.

In the application of complex pulse protocols or pulse sequences PS, as it is necessary for the induction of a plasticity change in a human brain, an adaptation of protocol parameters to the determined I-wave latency time during treatment produces a maximum effect.

FIG. 35 shows, by way of example, an operating sequence, as can be carried out in the case of the magnetic stimulator 1 according to the invention. The treatment of a patient P or the application to a tissue with a magnetic field within a so-called ^¬ session (session). At the meeting, a complex pulse sequence via the stimulation coil 4 is delivered to the to investi ^¬-reaching tissue. The complex pulse sequence PS consists in the simplest case of individual pulses or stimuli. Complex pulse sequences PS delivered within the session consist of pulse trains PZ. Pulse trains or trains PZ in turn consist of pulse bursts or pulse packets PP. The pulse bursts or pulse packets PP contain stimuli or pulses. A stimulus may be a single pulse, but also, as shown in FIG. 35, a multiple double pulse. The inventive Magnetsti- mulator 1, it is possible that a user configures a complex pulse sequence PS ^¬ individually. In one possible ^embodiment , after the configuration of a pulse, visually checking its pulse shape or after configuring a complex pulse sequence by the editor, checks whether the configured pulses or the configured pulse sequence PS is permissible.

FIG. 36 shows a display on a graphical user interface GUI for explaining the mode of operation of a user editor which can be used in the magnetic stimulator 1 according to the invention. In Fig. 36, a pulse is formed within a session or a session which consists of nine Einzelimpul ^¬ sen biphasic waveform. As shown in FIG. 36, a selection of the intensity I can take place in different variants. Furthermore, it is possible to set trigger times by the user. Gerpunkt at each set of Trig magnetic stimulator is one from a signal via an interface, which can be a recording device ge ^¬ uses to store the following to this stimulus Mus ^¬ kelantwort.

When the user Editor the pulse trains PZ and the pulse bursts may or pulse packets PP are each generated by a separate assisting ^¬ tenten. For example, in one

Dropdown box a "burst" for Pulspaket or "train" for pulse ^¬ zug be selected by the user. Pulse trains PZ basie ^¬ ren on pulse bursts and pulse packets PP based on stimuli. A session can be stored as a stimulus or pulse sequence PS and used in a burst designer of the user editor. In one possible embodiment, the user editor includes a stimulus designer, a pulse packet assistant PPA, and a pulse train assistant PZA. These wizards are particularly suitable when large intervals occur between individual pulses. Fig. 37 is a diagram in which a burst PP is added by the user in the displayed user editor.

FIG. 38 shows a diagram in which a pulse train PZ is added by the user via the slot splitter.

By way of example, FIG. 39 shows a stimulus designer for configuring a stimulus or pulse. The user has to change the Mög ^¬ friendliness, characteristics of the stimuli or pulses, for example, by clicking on "detail". For example, the user can set the start polarity or the period of the stimulus or pulse, or the respective shaft. Each formed or configured Stimulus or pulse may be stored in one possible embodiment and downloaded from this memory for further processing The pulse sequences PS may be evaluated for their effects on the patient P and / or for their pulse structures with measurement results

and / or effects on the patient.

FIGS. 40A, 40B show by way of example a pulse packet PP formed with a burst assistant PPA. 40B shows a pulse train PZ formed with a train assistant PZA. In another possible embodiment, a pulse shape of a pulse may be using a Pulsselektors as is exemplified Darge ^¬ represents in Fig. 41 to be configured. In the embodiment shown in Fig. 41, a selection screen is constructed in two parts. The pulse selector preferably runs directly on the device and serves to select the protocols stored on the device. As a result, an operation of the MagnetSimulators 1 is possible without connecting an external PC. In a left area, a pulse the image of the selection screen ^¬ is shown graphically in the right portion form are selected. Valid and invalid ^pulses can be marked accordingly in the selection tree in the left area. The times of the different pulses can also be displayed. The curve type, ie Spu ^¬ lenstrom, electric field or electric field gradient, can be selected by a drop-down menu.

With the help of a pulse designer, it is possible to assemble or define a pulse shape of the respective pulse.

 For example, Fig. 42 shows a composite pulse consisting of sine wave, two pauses and a negative half wave. By double clicking the duration of each section can be edited. The length of the different sections of the pulse can also be changed by dragging with a mouse.

The magnetic stimulator 1 according to the invention can be used to Magnetstimu ^¬ lation of an organic tissue. The magnetic stimulation is a non-invasive, almost painless

Method in which nerves of the tissue are influenced by a time-varying magnetic field by induction in their electrical activity. The nerves can acti ^¬ fourth or inhibited.

The stimulation coil 4 of the magnetic stimulator 1 is placed near ei ^¬ ner skin surface. The stimulation coil 4 generates a rapidly changing magnetic field over time, which penetrates into the tissue. This penetrating magnetic field induces induction into electrically conductive areas of the tissue. In other applications, it is also possible to introduce the stimulation coil 4 into the tissue. The use of the magnetic stimulator 1 according to the invention requires no special preparation of the skin surface of the Pa ^¬ tienten P. The magnetic stimulator 1 may generate a magnetic field which urges by clothing, hair, etc. therethrough and produces irritation. Even low-lying areas are the goal of reaching ^¬ bar, since the magnetic field by bone structures such as the skull, penetrating. The depths ^¬ reach is limited to a few centimeters. A successful stimulation depends on the strength and orientation of the Orien ^¬ induced by the stimulation coil 4

electric field and set on the magnetic stimulator 1 pulse shape. The determined stimulation thresholds are valid for an examination session or a session, since they depend strongly on the physiological condition of the respective patient (fatigue, nervousness or, for example, blood sugar levels).

In order to make the magnetic stimulation between different patients or test persons comparable, the stimulation intensity is preferably normalized with regard to the individual motor stimulation threshold. The motor threshold is defined as the minimum stimulus intensity sufficient to produce some muscle action potential in a relaxed muscle in at least half of the cases. The threshold obtained in the relaxed muscle is for this reason as motor resting threshold RMT (resting motor threshold) ^¬ be distinguished. The active motor threshold AMT (Active Motor Threshold) can be determined in the same way in the preloaded muscle and is usually 5 to 20% below the motor rest threshold RMT. The Mag ^¬ netstimulator 1 according to the invention allows the delivery of different, self-assembled pulse shapes. In one possible implementation form can be adjusted by means of a dial to a user interface of the magnetic stimulator 1, the intensity I of the stimulation pulses to be delivered. Furthermore, in one possible embodiment, a stored pulse shape can be selected by means of a selection switch via a pulse selector on a display.

In another embodiment, the repetition frequency or the repetition rate can be set with a further dial. In another embodiment, with another dial, the pulse duration, i. the maximum length of a pulse train to be delivered can be selected.

In a single-pulse operation of the magnetic stimulator 1, a single stimulation pulse is delivered with the selected pulse shape when pressing a button. In a repeating operation of the magnetic stimulator 1, a pulse train is output with the set repetition frequency or repetition rate, as long as a certain key is kept pressed.

In possible embodiments, by pressing a memory key by the user, the currently set values for the pulse intensity, pulse sequence, pulse duration duration and pulse shape can be stored. The stored values are also obtained when the magnetic stimulator 1 is switched off. This makes it possible, for example, after switching on the magnetic stimulator 1 quickly and easily retrieve a previously stored set of default settings. In one possible embodiment, the magnetic stimulator 1 changes to a standby mode if no control element has been actuated for a predetermined time. To terminate the standby mode of operation, any control element may be included. For example, be ^¬ on a front panel of the magnetic stimulator be ^¬ . As a result, the magnetic stimulator 1 is put into an operational state and a corresponding ^indicator light is lit.

To trigger single pulses of the magnetic stimulator 1 is turned on, it is checked whether a stimulation coil 4 is connected. It can then be selected on the Einstellele ^¬ ment the desired pulse intensity. Furthermore, a pulse frequency is set. By pressing a BE ^¬ special control element, such as a pneumatic foot switch, the stimulation coil 4 can be set or activated. By pressing a pulse button then a single pulse is delivered.

To design a pulse sequence, in particular a complex pulse sequence PS, it is possible, for example, to switch to a duration display ^mode , in which case a desired pulse repetition duration is subsequently selected. After pressing a pneumatic foot switch see to activate the stimulation coil 4, a pulse button can be actuated so that the desired pulse ^¬ quota is delivered to the patient P, as long as the respective button is pressed. Once the set pulse duration has been reached, the pulse output is automatically stopped, even if the button remains pressed.

The inventive magnetic stimulator 1, it is possible stimuli or pulses with a very high repetition rate to generate ^¬ Center. This is possible due to the fast reloading of the pulse losses. The magnetic stimulator 1 according to the invention can achieve repetition rates with a frequency of 1000 Hz and more. This offers the advantage of achieving significantly longer and more stable stimulation effects which are relevant in basic research as well as in a therapeutic application. Strong lasting effects are a prerequisite for therapeutic success in a patient P.

Fig. 43 shows a normal muscle potential for representing effects that can be achieved by repetitive stimulation. The vertical arrows indicate the magnitude of the effect, ie an increase means the increase in the excitability and a drop means the decrease in ^¬ He regbarkeit the brain. The illustrated horizontal arrows show the duration of the effect, which can be derived on individual muscles of the patient P and allows direct conclusions about the change in excitability. With the curve CTBS (Continuous Theta Burst), the effect is represented by a conventional conventional protocol with a fre ^¬ quency of a maximum of 50 Hz (T _ISI = 20 ms). The two other curves shown in FIG. 43 show examinations with so-called quattropulses carried out with the magnetic stimulator 1 according to the invention, which were carried out with a repetition rate of 200 Hz (tISI-5 ms) and a repetition rate of 20 Hz (tisi-50 ms). As can be seen from FIG. 43, the effect in the case of high-frequency stimulation with the aid of the magnetic stimulator 1 according to the invention is longer and more pronounced than in the case of a conventional stimulation form. In Fig. 43, pre means the state before stimulation, while post 1 to 4 means after stimulation in a time range of 0 to 60 min. The flexibility in setting the complex pulse patterns or pulse sequences PS is advantageous because an individual stimulation, which adapts to the physiological conditions of the subject or patient P, is made possible. One A concrete example of individualized stimulation using magnetic stimulation is stimulation adapted to the so-called I-wave, which was possible with conventional magnetic stimulators with only two pulses, whereby the observed effects only lasted very briefly. An adaptation of the application of the magnetic stimulation, in particular with several, in particular four to eight pulses, is relevant to the effects achieved, which can be greatly extended thereby and are more pronounced in their expression. Furthermore, the current flow direction within the brain or the tissue, which is determined by the pulse polarity, also has a relevant influence.

Fig. 44 is a diagram showing the effect of current flow reversal (which corresponds to a polarity change) in the stimulated brain, as is possible by the magnetic stimulator 1 of the present invention. FIG. 44 shows a so-called I-wave adapted stimulation with a frequency of 666 Hz. AP means a current flow in the brain, which is generated by transcranial magnetic stimulation TMS and flows from front to back. PA means a current flow flowing from the back to the front. The horizontal arrows in Fig. 44 show the duration of the effect and vertical Pfeiffer ^¬ le show the amount of the effect on. In Fig. 44 an environmental transport is the effect can be seen from a rise to a fall of ^¬ He regbarkeit of the brain in reverse polarity. Pre means a state before the intervention by means of high-frequency transcranial magnetic stimulation TMS. Post means a condition within 0 to 60 minutes after the start of the intervention.

Furthermore, experimentally, after application of a double sine wave, the same effects can be geren variability, as illustrated in Fig. 45. The shortness of these stimulation forms (about 2 minutes) make them practical for the examination of young patients or children. Fig. 45 shows the effects of a Vierfachstimula- tion at a double sine wave that can be achieved with the fiction, modern ^¬ magnetic stimulator. 1 Shown is also an I-wave adapted stimulation at a frequency of 666 Hz, ie a distance of the four pulses of 1.5 ms. The horizontal arrow indicates the duration of the effect, the vertical arrow the height of the effect. From Fig. 45, a very stable effect (increase in excitability of the brain) with a low variability can be recognized even in a measurement on only a few subjects P. Another decisive advantage of the invention

Magnetic stimulator 1 with flexibly configurable Pulssequen ^¬ zen is a customization of pulse shapes to the individual physiological characteristics of the patient P. For example, in children, the so-called motor threshold, which is a measure of brain excitability of the stimulated point higher than in adult patients. In pediatric neurological diagnostics and in basic research using conventional magnetic stimulators, this often leads to limited testing of very young subjects.

Fig. 46 is a diagram showing the motor threshold at different pulse shapes. The pulses are applied to the brain from front to back (in the brain) in the current flow direction AP or from front to back in the reverse current flow direction PA. In FIG. 46 it can be seen that the motor threshold of a pulse shape which is applied from front to back (AP) is longer than from Pulses that are applied from back to front (PA) or have a negative polarity.

The used in the novel magnetic stimulator 1 User editor with graphic interface allows an easy intuitive operation by the user and, in particular, a simple configuration of a pulse protocol or a com plex ^¬ pulse sequence PS. Furthermore, it is possible to carry out an automated adaptation to measured neurophysiological parameters by a feedback of the parameters to the magnetic stimulator 1. By using the Magnetstimu- lators 1 can be achieved greatly reduced interindividual Varia ^¬ bility of protocols and a stable induction of cortical plasticity with unique effects compared to already existing conventional protocols. These effective plasticity-inducing pulse protocols or pulse sequences PS allow a therapeutic intervention on the patient P to optimize his neuronal plasticity, especially in neurological and psychiatric disorders. Furthermore, the magnetic stimulator 1 according to the invention makes it possible to further investigate the human brain in order to obtain scientific knowledge.

Claims

Magnetic stimulator (1) for stimulating a tissue through a magnetic field with:

(A) a pulse generator means (2) having a

Pulse capacitor which is chargeable by a charging ^{scarf ¬} device (2a) for generating a pulse sequence consisting of pulses with an adjustable repeating rate; and with

(b) a programmable control device (3), the pulse generator means (2) for generating a complex pulse sequence (PS) having individually configurable pulses sets, wherein the gene ^¬ tured complex pulse sequence (PS) to a Stimulati ^¬ onsspule (4 ) is applied to generate the magnetic field.

Magnetic stimulator according to claim 1,

wherein the pulse sequence output by the pulse generator means (2) is a simple pulse sequence consisting of pulses or a complex pulse sequence comprising pulse trains (PZ) each comprising pulse packets (PP) each consisting of a train of pulses, one pulse shape and one pulse pulse / or polarity of the pulses is individually configurable.

Magnetic stimulator according to claim 1 or 2,

wherein the programmable control device (3) of the magnetic stimulator (1) via an interface (6) to a computer (7) can be connected, on which a user editor for configuring the pulse sequence (PS) is provided. Magnetic stimulator according to claim 3,

being the user editor of the magnetic stimulator

(1) connected to the computer (7) a stimulus Designer for configuring a pulse shape of the pulses, a pulse packet assistants (PPA) to the configuration of at least one consisting of pulses pulse packet and a Pulszügeas ^¬ sistenten (PZA) for configuring at least one of pulse packets (PP) existing pulse train ( PZ).

Magnetic stimulator according to one of the preceding claims 1 to 4,

wherein the configured by the user editor pulse ^¬ sequence (PZ) of the computer (7) via the interface (6) of the magnetic stimulator (1) to the programmable control means (3) of the magnetic stimulator (1) übertra ^¬ gene and in a storage unit of the magnetic stimulator (1) is stored.

Magnetic stimulator according to one of the preceding claims 1 to 6,

wherein the repetition rate of the pulse sequence (PS) indicates the number of pulses per second and is adjustable in a range of 0 to 1 kHz.

Magnetic stimulator according to one of the preceding claims 1 to 6,

wherein an evaluation pulse (EP) for measuring a motor muscle response of the stimulated tissue is delivered between pulse packets (PP) of the complex pulse sequence (PS) generated by the pulse generator means (2) of the magnetic stimulator (1).

8. Magnetic stimulator according to one of the preceding claims 1 to 7,

wherein said pulse generating means (2) of the Magnetst imula- tors (1) a resonant circuit which includes the pulse capacitor and the stimulation coil (4), and at least egg ^¬ NEN breaker which a by the programmable control means (3) of the magnetic stimulator (1) controllable driver circuit (TS) is connected, has.

9. Magnetic stimulator according to claim 8,

 wherein the stimulation coil (4) is connected in a full bridge with four circuit breakers for generating pulses whose pulse shape is composed of pulse segments.

10. Magnetic stimulator according to one of the preceding claims 1 to 9,

 wherein the pulse generator means (2) of Magnetst imula- sector (1) a charging circuit (2a) for reloading the

Pulse capacitor with the set Repetierrate on ^¬ points.

11. Magnetic stimulator according to claim 10,

 wherein the charging circuit (2a) of the pulse generator device (2) is a linear charging circuit comprising a power supply unit (NT) for connection to a power supply network,

an energy intermediate circuit (EZK) for temporarily storing the electrical energy supplied by the power supply and a charge controller (LR), which is connected to the resonant circuit of the pulse generator means (2).

12. Magnetic stimulator according to claim 10,

 wherein the charging circuit (2a) of the pulse generator means (2) is a clocked charging circuit which

a power supply (NT) for connection to a power supply ^¬ net,

 a first DC / DC switching regulator for continuous operation,

 a power link (EZK) for latching the one supplied by the first DC / DC switching regulator

 electrical energy and

 a second DC / DC switching regulator for pulse mode, which is connected to the resonant circuit of the pulse generator means (2).

13. Magnetic stimulator according to one of the preceding claims 1 to 12,

 wherein the pulse generator means (2) comprises a coil monitoring circuit (2c) which monitors whether a stimulation coil (4) is connected to the magnetic stimulator (1) and which has sensors for monitoring operating parameters of the stimulation coil (4).

14. Magnetic stimulator according to one of the preceding claims 1 to 13,

wherein said programmable control means (3), the pulse ^¬ generator means (2) for delivering the stimulation pulse sequence to the spool (4) only causing after a system check of parameters of the magnetic stimulator (1) has been successfully completed.

15. Magnetic stimulator according to one of the preceding claims 1 to 14,

wherein the programmable controller (3) to a attached to the fabric to be stimulated Ableitelekt ^¬ rode (10) for deriving a measurement signal and / or for generating a trigger signal can be connected.

16. Magnetic stimulator according to claim 15,

wherein the derived measurement signal is evaluated by the programmable ^{controller ¬} (3) for determining a motor threshold.

17. A method of generating a magnetic field with the crotch ^¬ th:

(a) generating a complex pulse sequence (PS) consisting of individually configured pulses having a variable pulse shape by a pulse generator means

(2);

(B) applying the generated pulse sequence (PS) with an adjustable repeating rate to a stimulation coil (4), which generates the magnetic field therefrom and

(C) recharging a pulse capacitor of the Pulsgenera ^¬ gate device (2) by a charging circuit (2a) with the set Repetierrate.

18. The method according to claim 17,

wherein the repetition rate indicates the number of pulses per second and in a range from 0 to 1 kHz is ^¬ adjusted.

19. The method according to claim 17 or 18,

wherein the generated complex pulse sequence (PS) comprises pulse trains (PZ) each comprising pulse packets which are each because they consist of a sequence of pulses whose pulse shape and / or polarity is configured individually.

Apparatus for use in a method of stimulating a tissue by a magnetic field,

wherein a complex pulse sequence (PS), which consists of individually configured pulses with variable pulse shape, by a pulse generator means (2) which applies the pulse sequence (PS) with an adjustable high repetition rate to a stimulation coil (4), from which the magnetic field generated,

wherein a pulse capacitor of the pulse generator means (2) is recharged by a charging circuit (2a) with the set repeating rate.