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WO2010139376A1 - Dispositif et procédé d'excitation des nerfs par des impulsions de champ magnétique - Google Patents

Dispositif et procédé d'excitation des nerfs par des impulsions de champ magnétique Download PDF

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Publication number
WO2010139376A1
WO2010139376A1 PCT/EP2010/001622 EP2010001622W WO2010139376A1 WO 2010139376 A1 WO2010139376 A1 WO 2010139376A1 EP 2010001622 W EP2010001622 W EP 2010001622W WO 2010139376 A1 WO2010139376 A1 WO 2010139376A1
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WIPO (PCT)
Prior art keywords
coil
current
magnetic field
pulse
pulses
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PCT/EP2010/001622
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German (de)
English (en)
Inventor
Stefan M. Götz
Thomas Weyh
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Technische Universität München
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Publication of WO2010139376A1 publication Critical patent/WO2010139376A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N2/00—Magnetotherapy
    • A61N2/02—Magnetotherapy using magnetic fields produced by coils, including single turn loops or electromagnets
    • H—ELECTRICITY
    • H03—ELECTRONIC CIRCUITRY
    • H03K—PULSE TECHNIQUE
    • H03K17/00—Electronic switching or gating, i.e. not by contact-making and –breaking
    • H03K17/13—Modifications for switching at zero crossing
    • H03K17/136—Modifications for switching at zero crossing in thyristor switches

Definitions

  • the present invention relates generally to a device for nerve and muscle stimulation according to the principle of inductive magnetic stimulation by pulsed magnetic fields. Furthermore, the invention relates to electrical power circuits for generating improved timing of pulse-shaped magnetic fields for nerve irritation.
  • certain cells can be irritated by externally applied electric fields in the body tissue. This happens because the electrical fields in the tissue cause electrical currents, which in turn trigger action potentials in these cells, for example in nerve or muscle cells.
  • the principle of magnetic induction can also be used for this type of irritation.
  • a time-varying magnetic field generates an induced electric field.
  • the time-varying magnetic field can be generated by a coil, which is traversed by a time-varying current.
  • This coil, the treatment coil for example, rests on the skin above the nerve tissue to be stimulated, so that the magnetic field generated can penetrate the tissue and generates the currents required for the stimulation in the tissue according to the induction principle.
  • the stimulation by this so-called inductive magnetic stimulation can be done without contact, since the magnetic field can penetrate body tissue unhindered.
  • the time-dependent magnetic fields are generated via short current pulses of a duration of usually 50-400 microseconds.
  • Figure 1 shows a typical arrangement of the use of inductive magnetic stimulation.
  • the pulse source 110 generates a short strong current pulse and conducts it to the treatment coil 120.
  • the treatment coil 120 is positioned close to the irritant nerve tissue of the body so that the generated magnetic field can penetrate this tissue structure.
  • the magnetic field generated by the coil induces an electrical field in the body tissue, here on the upper arm 130, which excites nervous and muscular tissue via the resulting currents.
  • FIG. 2 shows the basic circuit structure of an inductive stimulation device, as it was used in the first devices in particular for contactless irritation of cortical nerve structures through the intact skull bone.
  • the circuit uses a powerful damped electrical resonant circuit (resonator) consisting of a capacitor 220, a damping resistor 230, a diode 240, a thyristor 250 and the treatment coil 260.
  • the charging circuit 210 charges the capacitor 220 to a voltage of several thousand volts.
  • the energy content of the capacitor is several hundred joules.
  • the thyristor 250 serves as a switch that ignites the capacitor 220 with the magnetic! Beha ⁇ dlungsspuie 260 connects and so start the flow of current in the coil.
  • Figure 3 shows the time course of current and voltage in the treatment coil according to the circuit of Figure 2.
  • the typical time between the thyristor ignition and the achievement of the current peak value is about 50 to 150 microseconds.
  • This damping circuit used in the first devices which attenuates the oscillation from the first falling current edge (after one quarter of the period), characterizes the so-called monophasic stimulation, since the coil current only flows in one direction during the pulse, ie does not change its sign.
  • inductive magnetic stimulation the contactlessness, since the magnetic field of the treatment coil body tissue also reaches a certain distance from the coil. Therefore, nerve cells can also be irritated sterile.
  • the method in contrast to electrical stimulation via electrodes, the method is almost completely free of pain since, unlike electrostimulation, high current densities can not occur at feed locations of electrodes. For these reasons, this method is also particularly well suited to irritate deep tissue structures (eg the cerebral cortex through the skull bone) and for painless muscle stimulation eg in the field of rehabilitation.
  • this detour via the magnetic field of the treatment coil also has important technical problems:
  • the required magnetic flux densities are in the range of approximately 1 Tesla, so that high field energies must be conducted into the coil. Therefore, during the very short magnetic stimulation pulse, extremely high electrical power must be introduced into the coil; this power can reach values of several megawatts. Furthermore, since the pulse energy of the magnetic field is completely lost with the first devices at every pulse, these devices consume very high energy. Furthermore, the treatment coil overheats in this device technology very quickly, in which case it must also be noted that the coils may not reach too high temperatures as a treatment part, which can touch the body directly.
  • a further disadvantage is that the time course of the current induced in the tissue and used for the stimulation, in contrast to electrostimulation, can no longer be freely selected.
  • an electric field is induced according to the principle of magnetic induction only when the coil current and thus the magnetic field changes over time.
  • these first devices are not suitable for the so-called repetitive stimulation, in which 10 to 50 pulses per second are required.
  • This repetitive stimulation is used, for example, in neuro-rehabilitation for relearning movement patterns or for building muscle.
  • the size of the devices and their high price make it difficult to open up further fields of application in neurodiagnosis and neurorehabilitation.
  • FIG. 4 shows the basic circuit structure of a stimulation device which generates sinusoidal current or field pulses. Again, the charging circuit 210 charges the
  • Capacitor 220 to a voltage of several thousand volts.
  • the thyristor 410 serves again as a switch, the capacitor 220 with the magnetic when ignited
  • Treatment coil 260 connects. Unlike the monophasic
  • Coil voltage of the resonant circuit continues to oscillate.
  • FIG. 5 shows the time course of current and voltage in the treatment coil according to the circuit of Figure 4.
  • the advantage of this circuit principle according to FIG. 4 is that a large part of the field energy used for the treatment coil 260 can be returned to the capacitor 220, thus reducing the losses both in the pulse source and in the treatment coil 260.
  • the losses of the circuit of Figure 4 are mainly due to the ohmic resistances of the circuit components involved and their connection cable.
  • capacitor 220 since the current amplitude required for successful stimulation is approximately unchanged from monophasic pulse form devices, the necessary voltage and energy content of capacitor 220 also remain nearly the same, as in monophasic devices.
  • FIG. 6 illustrates a further development of the circuits of inductive magnetic stimulators.
  • the charging circuit 210 charges the capacitor 220 to a voltage of several thousand volts.
  • the thyristor 610 again serves as a switch which connects the capacitor 220 to the magnetic treatment coil 260 during ignition.
  • Figure 7 shows the time course of current and voltage in the treatment coil according to the circuit of Figure 6.
  • the second thyristor 620 can also be ignited directly upon reaching the first current zero point, so that a full sinusoidal oscillation arises, similar to FIG. 5. In any case, however, the field energy of the coil is also returned to a large extent back into the capacitor in this circuit.
  • biphasic full-wave stimulation duration of the current pulse a full sine period
  • biphasic half-wave stimulation A disadvantage of the biphasic half-wave stimulation, however, is that after the pulse, the voltage direction in the capacitor is inverted compared to the state before the pulse output, whereby the corresponding charging circuit becomes more complex. Furthermore, in the case of biphasic half-wave stimulation, the direction of the magnetic field also changes, so that successive pulses easily produce different effects in the tissue.
  • Coil heating is due to the very high required coil currents in the kiloampere range and the weight reasons, not arbitrarily reducible
  • the inductive magnetic stimulation could be compared to the Electrical stimulation already enforce in some areas or even open up new application areas.
  • inductive magnetic stimulation is also used in basic research as a tool for joint examination together with functional magnetic resonance tomography.
  • Pulse can be used to generate specific stimulation (and inhibition) of certain areas of the brain, the effects of which can in turn be investigated with this imaging method.
  • peripheral motor nerves are activated and trained for muscle building and / or the re-learning of specific movement patterns.
  • repetitive continuous stimulation with fast pulse sequences about 10 to 50 pulses per second
  • the described power and energy problems of previous devices become even clearer.
  • the devices are already very often used to build muscle after injury or to use the usual training effect (especially in many top athletes).
  • the force effect achievable on the muscle via the inductive magnetic stimulation has so far not been comparable with the willfully achievable force for purely technical-physical reasons.
  • the invention is based on the finding that with an improved adaptation of the time-course of the currents induced in the tissue to the dynamic charge-transport phenomena of the nerve fibers, the required field strength and field energy for inductive irritation can be reduced.
  • the time course of the short magnetic field pulse generates the treatment coil to change over previous systems in such a way that the mean edge steepness rising edges of the induced electric field differs from the mean edge steepness sloping edges.
  • the magnetic stimulation pulses produced by the power electronics according to the invention should no longer have a sinusoidal or attenuated sinusoidal profile, but be such that the electric field induced by the coil either increases significantly faster than it drops or increases significantly more slowly than it does drops.
  • the course of the induced from the treatment coil electric field follows approximately the time course of the coil voltage. Accordingly, the mentioned time dependencies of the course of the induced electric field can be achieved via a corresponding course of the coil voltage.
  • the field pulses generated by the treatment coil can be designed so that only one rising and one falling edge of the induced electric field strength are generated or alternating within a pulse a plurality of rising and falling edges of the induced field strength, in each case in this case clearly distinguish the average edge steepnesses of the rising flanks from the mean edge steepnesses of the falling flanks.
  • the associated power electronics can be designed so that in each case takes place at the zero crossing of the coil current, a brief interruption of the oscillation process. During these interruption times, no magnetic field is generated by the coil.
  • the power electronics should be designed so that the power electronics together with the treatment coil represents a resonant system of one or more resonant circuits.
  • the field energy of the coil can be returned to one or more capacitors.
  • pulses can be generated which are composed of individual sections of sinusoids of different frequencies.
  • the pulses can be shaped so that the mean edge steepness of the rising edge clearly differs from the mean edge steepness of the falling edge.
  • the magnetic Feide ⁇ ergie the treatment coil can be energy-efficiently fed back into one or more capacitors of the power electronics to a large extent.
  • An advantage of the present invention is the provision of an apparatus and method for inductive nerve stimulation which require relatively low field energy and field strength to irritate the nerves. With this reduction of energy and the one or more capacitors used for the intermediate storage of the pulse energy can be reduced in terms of their sizes.
  • Another advantage of the present invention is the provision of an inductive nerve stimulation device and method which requires a comparatively lower capacitor and coil voltage for the irritation of the nerves so that isolation distances can be reduced and necessary safety measures can be simplified.
  • Another advantage of the present invention is the provision of an inductive nerve stimulation apparatus and method which requires a relatively low coil current for stimulus initiation.
  • the current heat losses in the treatment coil and in the supply cable can be reduced, on the other hand can be used in the power circuit used for pulse power electronic Leist ⁇ ngsbaumaschine of comparatively lower current carrying capacity and correspondingly smaller size.
  • Another advantage of the present invention is to provide a device and a method for inductive nerve stimulation, which is due to their relatively low energy consumption, especially for repetitive stimulation with pulse repetition rates of 10 to 1000 pulses per second.
  • the devices for pulse generation according to the invention can be made comparatively small, lightweight and thus portable.
  • Another advantage of the present invention is the provision of an apparatus and method for efficiently generating non-sinusoidal time courses of the magnetic field pulses with simultaneously high power and low power Losses.
  • the mean edge steepness of the rising edge of the coil voltage can be controlled independently of the mean edge steepness of the falling edge and thus also of these edges of the tissue induced voltages and currents in the tissue.
  • FIG. 1 shows a pulse source, the treatment coil coupled via a cable and the tissue structure to be stimulated (human upper arm);
  • Fig. 2 shows the basic structure of a monophasic power circuit
  • Fig. 3 shows the voltage and current waveform in the coil of a monophasic stimulator during a pulse
  • Fig. 4 shows the basic structure of a power circuit for generating full sine waves
  • Fig. 5 shows the voltage and current waveform of a full-wave stimulator in the coil during a pulse
  • Fig. 6 shows the basic structure of a power circuit for generating sinusoidal half-waves
  • Fig. 7 shows the voltage and current waveform of a half-wave stimulator in the coil during a pulse
  • Fig. 8 shows by way of example the time course of the coil current I L and the coil voltage, which is composed of two juxtaposed sine half-waves of different frequency;
  • Fig. 9 shows the change of the triggering threshold for a nerve fiber as a function of the quotient of the frequencies of two juxtaposed half-waves of different frequency according to Fig. 8;
  • Fig. 10 shows by way of example a power circuit according to a first embodiment of the present invention
  • Fig. 11 shows by way of example the time course of the coil current I L and the coil voltage U 1 according to the first embodiment of the invention
  • Fig. 12 shows by way of example a power circuit according to a second embodiment of the present invention.
  • Fig. 13 shows by way of example the time course of the coil current IL2 and the coil voltage U L according to the second embodiment of the invention
  • Fig. 14 shows by way of example a power circuit according to a third embodiment of the present invention.
  • Fig. 15 shows by way of example the timing of the coil current IL and the coil voltage UL according to the third embodiment of the invention.
  • Fig. 16 shows by way of example a power circuit according to a fourth embodiment of the present invention.
  • Fig. 17 shows by way of example the time characteristic of the coil current I Ln and the coil voltage U L according to the fourth embodiment of the invention.
  • Fig. 18 shows by way of example a power circuit according to a fifth embodiment of the present invention.
  • Fig. 19 exemplifies a power circuit according to a sixth embodiment of the present invention.
  • Fig. 20 shows by way of example the time course of the coil current I L and the coil voltage U L according to the sixth embodiment of the invention.
  • the invention is based on the finding that the strength and energy of the magnetic field pulse required for nerve stimulation can be significantly reduced if the temporal current profile is adapted to the dynamic behavior of the ion transport processes in the nerve cell membrane.
  • this can be achieved if the associated power electronics for pulse generation the time course of the short Magnetic field pulse, which generates the treatment coil, compared to previous systems changed in such a way that the mean edge steepness of the rising edge of the induced electric field differs significantly from the mean edge steepness of the falling edge.
  • This in turn is achieved when the time course of the coil voltage generated by the power electronics is such that the mean edge steepness of rising edges clearly differs from the mean edge steepness of falling edges.
  • the power electronics can generate pulses which have a plurality of voltage zero crossings and thus also a plurality of rising and falling edges of the time profile of the induced electric field strength during a single pulse and thereby also the respective mean edge steepnesses of rising edges from the mean edge steepnesses clearly distinguish between sloping flanks.
  • the associated power electronics can be designed so that during a pulse at least one zero crossing of the coil current takes place a short interruption of the oscillation process. During these interruption times, no magnetic field is generated by the coil.
  • the knowledge of the necessary temporal course of the field is based on a mathematical modeling of the nerve cells, as first established by Hodgkin and Huxley (AL Hodgkin, AF Huxley: Quantitative Description of Membrane Current and its Application to Conduction and Excitation in Nerve Journal of Physiology 117, 1952, pp. 500-544).
  • the model is based on a set of nonlinear differential equations and simulates the behavior of nerve cells, especially the behavior of axons. For example, this model models the response of an axon to external electrical currents. Therefore, the required stimulus currents can be computationally determined with different pulse shapes, which are necessary in order to trigger an action potential in the nerve cell.
  • the model incorporates the dynamic, nonlinear behavior of, for example, the sodium and potassium ion channels of the cell membrane into the simulation.
  • Such models describe the temporal behavior of neurons with nonlinear terms of high order. Direct inversion of the equations is therefore generally not possible. Optimizations must therefore be made via skillful estimates with subsequent quantitative confirmation in the forward model.
  • it can be deduced from the model that there exists both an underlying mechanism that favors the induction of an action potential and an inhibitory mechanism that tends to suppress triggering. These two mechanisms have a very different time behavior, which can be exploited for the optimization of particularly energetic stimuli.
  • the amplitude of the current required for an irritation current pulse can be reduced if the mean slope of the rising edge of the time course of the stimulus current is significantly higher than the mean edge steepness of the falling edge, or more generally when the mean edge steepness of the rising edge significantly different from the mean edge steepness of the falling edge.
  • the stimulation current in the tissue follows approximately the course of the induced by a stimulation coil in the tissue electric field strength.
  • the course of this induced electric field strength in turn directly follows the course of the voltage in the treatment coil. Therefore, for an optimization of the stimulus pulse, the average slope of the rising edge of the coil voltage should be significantly different from the mean slope of the falling edge.
  • stimulus pulses are also particularly efficient if several rising and falling edges of the time course of the coil voltage alternate in rapid succession, whereby in turn the respective mean edge steepnesses of the rising edges of the coil voltage are dependent on the mean edge steepnesses of the coil voltage clearly distinguish between sloping flanks.
  • An electronic circuit according to the invention which generates pulses with the properties described above, requires a lower magnetic field strength for the treatment coil and thus also a lower field energy for stimulus triggering in comparison to previous systems for inductive magnetic stimulation. Accordingly, it also allows the required coil current and thus the losses of the coil, and their heating can be reduced. By reducing the field energy, the coil voltage required for the stimulation can furthermore be reduced.
  • the circuit for generating the optimized coil pulses according to the invention generates current pulses in the treatment coil, which are composed of two sine half-waves of different frequency, wherein the first half wave sinusoidally rising current (and thus with maximum Coil voltage) begins and the transition from the first half-wave to the second takes place in the current zero crossing.
  • a sine wave is defined as a time course of the respective variable in the form of a sine function.
  • the course may also be slightly damped, i. the amplitude of the wave decreases slightly with increasing time.
  • a full sine wave is defined as a time characteristic of the respective quantity in the form of a sine function over a full period, ie sin (x) for 0 ⁇ x ⁇ 2 ⁇ .
  • a sine half-wave is defined as a time characteristic of the respective quantity in the form of a sine function over half a period, ie sin (x) for 0 ⁇ x ⁇ ⁇ .
  • the circuit generates current pulses in the treatment coil, which are composed of several sections of sine waves, each having a different frequency, so that the respective mean edge slopes of rising edges of the coil voltage clearly differ from the mean edge slopes sloping edges.
  • the circuit generates current pulses in the treatment coil, which are composed of two or more juxtaposed sinusoidal half waves with the same polarity, since here too mean edge slopes of the rising edges of the coil voltage resulting from the mean edge slopes of the clearly distinguish between sloping flanks.
  • FIG. 8 shows, by way of example, a time profile of the spin current I L and of the coil voltage U L , which are composed of two sinusoidal half-waves of different frequencies. The induced in the tissue electric field strength and the resulting current follow approximately the course of the coil voltage U L.
  • FIG. 9 shows the result of a computational simulation in which the current amplitude required for an irritation was investigated for different pulse shapes.
  • the pulse duration ie the total time for the two sinusoidal half-waves juxtaposed, as shown in FIG. 8, was kept constant.
  • the quotient consisting of the duration of the first half-wave through the duration of the second half-wave, was varied.
  • the relative threshold current that is currently required for a depolarization ie for the triggering of an action potential in the nerve fiber (axon) was determined. This current amplitude is also called the triggering threshold.
  • the maximum induced tissue flow is directly proportional to the maximum coil current and to the maximum capacitor voltage, a change in this triggering threshold is a crucial value for the effectiveness of the inductive stimulus devices.
  • the required pulse energy can even be reduced to less than 25% due to this improved pulse shape. Since the ohmic current heat losses of the resonant circuit also depend on the square of the current, the losses and the coil heating in this example can be reduced to less than 25%. Conversely, if this quotient is reduced, the stimulus threshold is increased in comparison with an irritation with full-wave sine waves.
  • pulses which are composed of more than two juxtaposed half-waves with the current curves shown in Figure 8
  • a further increase in efficiency over the single wave shown here is possible.
  • This application of pulses with the described courses of events can be used as a method of irritating nerve and muscle cells.
  • a method according to the present invention may also be used for non-therapeutic purposes.
  • such a method can be used for targeted muscle building or the representation of functional relationships of the neuromotor system in humans and animals.
  • the duration of the magnetic field pulses are approximately in the range of 20 to 3000 microseconds; preferably, the duration should be in the range of 100 to 500 microseconds.
  • the strength of the magnetic field pulses should be at the coil surface in the range of a flux density of 0.1 to 5 Tesla.
  • the magnetic flux density should be in the range of 0.3 to 1 Tesla.
  • This electrical stimulation current in the tissue should be at least one-tenth and a maximum of five times the stimulus currents required for irritation of the cells.
  • the stimulation current should be at least half and at most twice the stimulation currents needed to stimulate the cells.
  • time courses of the coil current pulse can be generated, which are composed of parts of sine waves of different frequency.
  • time courses of the coil current are realized by means of switchable capacitors and / or switchable coils, the inductance of the treatment coil remaining unchanged.
  • These resonant circuit elements can therefore define either successively or simultaneously the current flow in the power circuit and in particular in the treatment coil.
  • FIG. 10 shows a first embodiment of the invention for generating pulse shapes according to FIG. 8.
  • This circuit is based on a direct coupling of two oscillating circuits, which alternately or at times simultaneously determine the time characteristic of the coil current and the coil voltage.
  • the resonant circuits use a common coil 1010, namely the treatment coil, but each use their own capacitors 1030 and 1050 with different capacitance.
  • a capacitor 1030 or 1050 forms with an associated circuit breaker 1020 and 1040, a capacitor-switch unit.
  • the two capacitor switch units are alternately or temporarily also electrically connected to the coil 1010 so that a switching between the capacitors is preferably carried out during the zero crossing of the coil current.
  • a current waveform can be generated on the coil, which consists of two sine half-waves of different frequency (or of several sections of waves with different frequencies).
  • the sinusoidal half-waves of different frequency can also be generated so that during a half cycle both capacitors 1030 and 1050 are connected to the coil 1010, and during the other half wave only one of the two capacitors 1030 or 1050 is connected to the coil 1010.
  • capacitors of the same capacity can be used.
  • the two switches 1020 and 1040 can either be controlled so that a single full wave of the coil current (which is composed of two individual half-waves of different frequencies or multiple sections of waves with different frequencies) arises or that produces more than two directly juxtaposed half-waves become.
  • FIG. 11 shows, by way of example, such a time characteristic of the current I L in the treatment coil and the coil voltage U L , as achieved with the circuit according to FIG.
  • FIG. 12 shows a second embodiment, which is likewise based on the direct coupling of two oscillating circuits, which alternately or at times also simultaneously
  • the resonant circuits use a common capacitor 1250, but use their own
  • Coils 1210 and 1220 with different inductance wherein one of these coils the
  • Treatment coil is.
  • the two coil-switch units are alternately electrically connected to the capacitor 1250 so that switching from the first Coil to the second coil is preferably carried out during the zero crossing of the coil current.
  • a current waveform can be generated on the coil, which is composed of two sine half-waves of different frequency.
  • the sinusoidal half-waves of different frequency can also be generated so that during a half-wave both coils 1210 and 1220 are connected to the capacitor, and during the other half-wave only one of the two coils is connected to the capacitor.
  • coils of the same inductance can also be used.
  • the two switches 1230 and 1240 can either be controlled so that a single full wave of the coil current (which is composed of two individual half-waves of different frequencies or multiple sections of waves with different frequencies) arises or that produces more than two directly juxtaposed half-waves become.
  • FIG. 13 shows, by way of example, such a time characteristic of the current I L in the treatment coil and the coil voltage U L , as achieved with the circuit according to FIG.
  • FIG 14 shows a third embodiment, which is based on the direct coupling of several resonant circuits, which alternately determine the time course of the coil current and the coil voltage.
  • the resonant circuits use a common coil 1410, namely the treatment coil, but each use a plurality of own capacitors (n capacitors, where n> 1, of which only two, the capacitors 1430 and 1450 are shown), preferably with different capacitance.
  • a respective capacitor 1430 or 1450 forms one of a total of n capacitor-switch units with an associated power switch 1420 or 1440.
  • These capacitor switch units are alternately or temporarily also electrically connected to the coil 1410 so that switching from a capacitor to a next capacitor is preferably carried out during the zero crossing of the coil current.
  • a current waveform can be generated in the treatment coil, which is composed of several sine half-waves of different frequency.
  • the sine half-waves of different frequency can also be generated so that during a half-wave, a first group of capacitors is connected to the coil, and during a following half cycle one or more capacitors are connected to the coil, so that their total capacity different from the total capacity of the first group of capacitors. In this Case, capacitors of the same capacity can be used.
  • the switches 1420, 1440 can either be controlled so that a single case of the coil current (which is composed of two individual half-waves of different frequencies or multiple sections of waves with different frequencies) arises or that more than two directly juxtaposed half-waves are generated ,
  • FIG. 15 shows, by way of example, such a time characteristic of the current I L in the treatment coil and the coil voltage U L , as achieved with the circuit according to FIG.
  • Figure 16 shows a fourth embodiment, which is also based on the direct coupling of several resonant circuits, which alternately determine the time course of the coil current and the coil voltage.
  • the resonant circuits use a common capacitor 1650 for this purpose, but use several coils (n coils, with n> 1, of which only two, the coils 1610 and 1620 are shown), preferably with different inductance, one of these coils being the treatment coil.
  • a coil 1610 or 1620 forms with an associated circuit breaker 1630 or 1640 one of a total of n coil-switch units.
  • coil-switch units are alternately or temporarily also so electrically connected to the capacitor 1650 that a switch from one coil to the next coil is preferably carried out during the zero crossing of the respective coil current.
  • a current waveform can be generated in the treatment coil, which is composed of several sine half-waves of different frequency.
  • the sine half-waves of different frequency can also be generated so that during a half-wave, a first group of coils is connected to the capacitor, and during another half-wave, one or more coils are connected to the capacitor, so that their total inductance different from the total inductance of the first group of coils.
  • coils of the same inductance can also be used.
  • FIG. 17 shows by way of example such a time characteristic of the current I Ln in the nth coil, the treatment coil and the coil voltage UL, as achieved with the circuit according to FIG.
  • Figure 18 shows a fifth embodiment based on a combination of the third and fourth embodiments.
  • the resonant circuits use m capacitors and n coils, where m and n are integers greater than one.
  • the capacitors have been extended by further switches, so that in each case the current and voltage direction can be switched at the capacitors.
  • this switching can also take place on the coils (of which only two, the coils 1810 and 1820 are shown), if they are each extended by correspondingly more switches.
  • a changeover takes place from one coil to the next, or from one capacitor to the next, during the zero crossing of the respective current to be switched.
  • the switches 1830, 1840, 1850 and 1860 can either be controlled so that a single full wave of the coil current (which is composed of two individual half-waves of different frequencies or multiple sections of waves with different frequencies) arises or that more than two directly strung half waves are generated.
  • FIG. 19 shows a sixth embodiment which comprises a capacitor 1920 as a first energy store, which can be supplied with energy by an external charging circuit 210, and a coil 1910, preferably the treatment coil as a further energy store, which is connected to the first energy store via a special triggering circuit is.
  • the special trigger circuit consists of four switching elements 1930, 1940, 1950 and 1960, which on the one hand initiate the discharge of the first energy storage in the further energy storage, as well as again allow a recharge in the first energy storage.
  • the switches are preferably switched in pairs, so that each opposite switch closed and the remaining switches are open. A switch from one pair of switches to the other is preferably carried out at the zero crossing of Spuienstromes.
  • this Ausmolu ⁇ gsform generates temporal current curves in the treatment coil in such a way that a time course of the induced electric field strength results, in which the mean edge steepnesses of the rising edges of the mean edge steepnesses of the falling edges significantly different.
  • FIG. 20 shows, by way of example, such a time characteristic of the current I L in the treatment coil and the coil voltage U L , as achieved with the circuit according to FIG. 19.
  • the switches can be further controlled so that the one or more capacitors are each operated only in a polarity direction of the voltage.
  • care must be taken in particular during the discharging processes of the respective capacitor occurring within the pulses that the current direction across the switches is reversed at the latest when the capacitor is completely discharged, so that the capacitor voltage does not assume negative values, but instead instead continues to increase to positive values.
  • This periodic recharge can be via another electrically coupled Oscillating circuit system consisting of at least one switch, at least one further coil and at least one further capacitor.
  • the switches can be designed as power semiconductors, such as, for example, thyristors, IGBTs or MOSFETs.
  • the switches can additionally have a rectifying characteristic, so that they are either reverse-conducting or reverse-blocking.
  • these switches can also act as self-activating erasers, for example by increasing their conductivity when applied current or voltage characteristics have certain properties. This includes, for example, the polarity or a rapid increase in voltage.
  • switch power semiconductors with controllable electrical resistance such as IGBTs or MOSFETs can be used so that the current profile in the treatment coil can be controlled in addition to this controllable electrical resistance.

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  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Magnetic Treatment Devices (AREA)

Abstract

L'invention concerne un dispositif destiné à produire de courtes et fortes impulsions de courant dans une bobine, la bobine générant des impulsions de champ magnétique d'une durée de 20 à 3000 microsecondes et d'une intensité de 0,1 à 5 Tesla, qui engendrent, selon le principe de l'induction électromagnétique dans le tissu corporel, des courants d'excitation électriques destinés à exciter des cellules nerveuses et/ou musculaires, le dispositif contenant au moins un condensateur pour stocker et fournir l'énergie requise pour les impulsions de champ et un circuit de charge approprié pour charger ce condensateur et la bobine étant réalisée de manière à pouvoir être positionnée suffisamment près du tissu corporel à exciter de sorte que le champ magnétique généré par la bobine dans la zone cible prévue diminue au maximum à un dixième de l'intensité sur la surface de la bobine et les courants d'excitation électriques engendrés par le champ magnétique de la bobine se situent au minimum au dixième et au maximum au quintuple des courants d'excitation requis pour une excitation des cellules. Le dispositif dans la bobine peut générer une impulsion de courant dont la durée est conçue de telle manière qu'un champ électrique soit induit par la bobine, champ électrique dont la pente moyenne des flancs montants se différencie de la pente moyenne des flancs descendants.
PCT/EP2010/001622 2009-06-04 2010-03-15 Dispositif et procédé d'excitation des nerfs par des impulsions de champ magnétique WO2010139376A1 (fr)

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DE102009023855A DE102009023855B4 (de) 2009-06-04 2009-06-04 Vorrichtung zur Nervenreizung mit Magnetfeldimpulsen
DE102009023855.7 2009-06-04

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WO2016055201A1 (fr) * 2014-10-08 2016-04-14 Continental Automotive Gmbh Circuit d'attaque destiné à une inductance
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US11185690B2 (en) 2016-05-23 2021-11-30 BTL Healthcare Technologies, a.s. Systems and methods for tissue treatment
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