WO2003084605A1 - Procede et dispositif permettant de prevenir une crise epileptique - Google Patents

Procede et dispositif permettant de prevenir une crise epileptique Download PDF

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Publication number
WO2003084605A1
WO2003084605A1 PCT/EP2003/003543 EP0303543W WO03084605A1 WO 2003084605 A1 WO2003084605 A1 WO 2003084605A1 EP 0303543 W EP0303543 W EP 0303543W WO 03084605 A1 WO03084605 A1 WO 03084605A1
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WO
WIPO (PCT)
Prior art keywords
transmitter
seizure
seizure model
early warning
intervention
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Application number
PCT/EP2003/003543
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German (de)
English (en)
Inventor
Oliver Holzner
Original Assignee
Oliver Holzner
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Oliver Holzner filed Critical Oliver Holzner
Priority to JP2003581842A priority Critical patent/JP2005528141A/ja
Priority to AU2003226786A priority patent/AU2003226786A1/en
Priority to EP03745788A priority patent/EP1492593A1/fr
Publication of WO2003084605A1 publication Critical patent/WO2003084605A1/fr
Priority to US10/958,842 priority patent/US20050107655A1/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36014—External stimulators, e.g. with patch electrodes
    • A61N1/36025—External stimulators, e.g. with patch electrodes for treating a mental or cerebral condition
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/16—Devices for psychotechnics; Testing reaction times ; Devices for evaluating the psychological state
    • A61B5/165—Evaluating the state of mind, e.g. depression, anxiety
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/16—Devices for psychotechnics; Testing reaction times ; Devices for evaluating the psychological state
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/369—Electroencephalography [EEG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/40—Detecting, measuring or recording for evaluating the nervous system
    • A61B5/4076—Diagnosing or monitoring particular conditions of the nervous system
    • A61B5/4094—Diagnosing or monitoring seizure diseases, e.g. epilepsy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M21/00—Other devices or methods to cause a change in the state of consciousness; Devices for producing or ending sleep by mechanical, optical, or acoustical means, e.g. for hypnosis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N2/00—Magnetotherapy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/242—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents
    • A61B5/245—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents specially adapted for magnetoencephalographic [MEG] signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M21/00—Other devices or methods to cause a change in the state of consciousness; Devices for producing or ending sleep by mechanical, optical, or acoustical means, e.g. for hypnosis
    • A61M2021/0005—Other devices or methods to cause a change in the state of consciousness; Devices for producing or ending sleep by mechanical, optical, or acoustical means, e.g. for hypnosis by the use of a particular sense, or stimulus
    • A61M2021/0055—Other devices or methods to cause a change in the state of consciousness; Devices for producing or ending sleep by mechanical, optical, or acoustical means, e.g. for hypnosis by the use of a particular sense, or stimulus with electric or electro-magnetic fields
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/08—Other bio-electrical signals
    • A61M2230/10—Electroencephalographic signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/0404—Electrodes for external use
    • A61N1/0472—Structure-related aspects
    • A61N1/0476—Array electrodes (including any electrode arrangement with more than one electrode for at least one of the polarities)

Definitions

  • the invention relates to a method and a device for the automatic non-invasive controlled or regulated electromagnetic prevention of epileptic seizures in vivo.
  • the relevant technologies include the following approaches:
  • TMS transcranial magnetic stimulation
  • TMS for intervention in epilepsy consists of finding an epileptic focus based on the medical experience of the doctor using it, imaging procedures, or trying it out, and then trying to induce epileptic seizures with single or double coil systems (e.g. [5], [6 ], [10]).
  • WO 98/18394 describes a method with which magnetic stimulation is carried out on a subject, at the same time his brain activity is measured by means of an EEG. This known method is used for diagnosis.
  • WO 01/21067 discloses a method for the early detection of an impending epileptic seizure. This procedure is designed to predict an impending epileptic seizure for hours or days. This procedure measures a patient's brain activity at different locations before, during and after epileptic seizures. With the help of various nonlinear methods, sensor pairs are determined for this patient that predict the seizure particularly well in the context of a training phase consisting of seizures. Signal pairs are adapted at regular intervals, for which further attacks are necessary. The training and adaptation contained in this procedure prevent complete prevention, since the data must be updated again and again with new seizures.
  • the object of the present invention is to create a method and a device for the prevention of epileptic seizures.
  • the invention is based on the knowledge that the processes leading to epileptic seizures can be made quantifiable by naming suitable control parameters, so that reliable prevention is possible.
  • FIG. 1 shows a transmitter in a sectional view
  • FIG. 2 shows the transmitter from FIG. 1 in a view from below
  • FIG. 3 shows a planar projection of openings for sensors and transmitters according to their arrangement on a helmet
  • FIG. 4 shows a helmet and a carrier axis together with a chin rest
  • FIG. 5 shows a further planar projection of openings for sensors and transmitters according to their arrangement on a helmet
  • FIG. 6 shows an example of a time series of measured values of an EEG sensor
  • FIG. 7 shows a section of the time series from FIG. 6 in a phase space representation 8
  • FIG. 8 shows a typical course of the SNR (signal-to-noise ratio).
  • the device comprises a measuring system with apparatuses for electromagnetic measurement data acquisition, preprocessing and forwarding, for example in an advantageous embodiment comprising an EEG cap with its sensors, connections to the amplifier, amplifier, connections to the AD converter, ADC Converter, connections to the computer unit, electricity supplier for the apparatus, and connections.
  • apparatuses for electromagnetic measurement data acquisition for example in an advantageous embodiment comprising an EEG cap with its sensors, connections to the amplifier, amplifier, connections to the AD converter, ADC Converter, connections to the computer unit, electricity supplier for the apparatus, and connections.
  • the device comprises an actuating system with apparatus for the extracranial generation of magnetic fields, referred to as “transmitter”, and a device for converting the digital control or regulation specifications originating from the computer unit into transmitter signals, for example in an advantageous embodiment comprising current-carrying coils, power suppliers , Connections, D / A converter, together with connections.
  • Suitable sensors are EEG or MEG sensors.
  • the MEG sensors are formed, for example, from a SQUID sensor element with a suitable evaluation device for detecting a magnetic field and a cooling device.
  • the EEG sensors have, for example, two electrodes for measuring an electrical potential difference.
  • a sensor can have an electrical and / or magnetic shield from its surroundings, provided that its function is not hindered (for example, no shield in the direction of the patient's crane, but very well shield in the direction of other transmitters and / or sensors and / or connecting cable).
  • the part of the input side near the head can have a multiplicity of sensors which are distributed over the surface of the head near the brain; this multiplicity of sensors is referred to as a sensor grid.
  • the sensor grid has a fixing device for fixing the same with respect to the patient's crane, so that when the sensor grid is put on and taken off several times, the sensors return to their respective relative positions, for example by fitting the sensor grid into a helmet, the inside of which has the cranial shape of the respective patient replicates.
  • the fixation can also be carried out with the aid of a camera, the position of the patient's head in the room and the sensors with respect to the head being recorded by several cameras and converted in real time into 3D data.
  • An advantageous embodiment of the input side comprises its partially outpatient form, in which the measurement data is obtained via a portable sensor grid, which is connected to devices for measurement data preprocessing to be carried by the patient in a backpack or as part of the clothing, and in which the data transfer to the computer unit is advantageously wireless he follows.
  • a transmitter 5 comprises a current-carrying coil 6 with a para-, dia-, or ferromagnetic core 7, as shown in a sectional view in FIG. 1, the arrow directions symbolizing the directions of the current flow.
  • the transmitter 5 has essentially have a cylindrical shape, the outer surface and an end face of the cylinder forming the rear side being clad with a shield 8.
  • the coil 6 and the core 7 directly adjoin the side of the transmitter which is free of the shielding, and with this side the transmitter 5 is aligned with the cranium during operation to emit exogenous magnetic fields.
  • a holding element 9 is arranged, with which the transmitter 5 can be fixed in a home.
  • the extracranial transmitter 5 can be protected against deformation, for example by pouring the live parts into suitable resin or embedding the live parts in stable insulating material.
  • the transmitter 5 can be provided with a cooling device.
  • intracranially implanted electrodes are used as sensors and / or transmitters, via which both EEG measurements can be carried out and currents can be conducted into the brain.
  • Lines leading to these electrodes and / or their interfaces to the computer unit and / or further lines and / or further measuring devices and / or the associated computer unit and / or the energy supplier of electrodes and / or computer unit can also be implanted, thereby permitting outpatient operation.
  • An advantageous embodiment of the parts of the positioning system close to the head comprises a plurality of transmitters which are distributed intracranially or extracranially; this arrangement of transmitters is referred to as a transmitter grating.
  • An advantageous embodiment of an extracranial transmitter grating includes fixing it with respect to the crane of the respective user, so that when the transmitter grille is put on and taken off several times, the transmitters assume their respective relative positions again, for example by fitting the transmitter grille into a helmet, the inside of which is the cranial shape of the respective user replicates.
  • Another advantageous embodiment of the transmitter grid comprises implanted electrodes.
  • An advantageous embodiment of the parts of an extracranial measuring and positioning system close to the head comprises a helmet 10 on its inside which reproduces the cranial shape of the respective user, with connecting cables running through a support axis 11 and a chin rest 12.Sensor and transmitter grids in the interior of the helmet are fixed in such a way that both grids overlap - ie there are sufficient transmitters in the vicinity of each sensor and vice versa.
  • FIG. 3 shows a planar projection of the superimposition of the transmitter with the sensor grid (openings 13 for sensors are shown as circles and openings 14 for transmitters 5 as squares).
  • the user sits on an armchair with a neck support below the helmet 10.
  • the sensor grid is intracranial and the helmet contains the extracranial transmitter grid.
  • the transmitter grid is intracranial and the helmet contains the extracranial sensor grid.
  • both sensor and transmitter gratings are intracranial.
  • the sensor density or sensor configuration of an extracranial sensor grid can be set. In a further advantageous embodiment, this change is automated, controlled or regulated via the intermediate unit.
  • the transmitter density or transmitter configuration of an extracranial transmitter grid can be set and / or the angle of inclination of each individual transmitter to the patient's cranium can be changed.
  • FIG. 5 shows a planar projection of a mechanical holder of this embodiment. Openings 13 for sensors are circles and openings 14 for Transmitter shown square. Here it is possible to anchor transmitter 5 in the openings 14 of the holder and / or to tilt transmitter 5 with respect to the holder.
  • all conventional coil configurations can be represented with their arrangement, orientation and field direction.
  • the device is provided with conventional protection against power failures and / or voltage fluctuations.
  • the computer unit runs real-time and automatically: i) ongoing calculation of the seizure early warning indicator from the input data, ii) if the indicator exceeds thresholds, calculation of an intervention instruction to prevent seizure, and implementation of the intervention in question using the transmitter Magnetic fields, iii) If the indicator returns to normal and / or a time limit is exceeded, shutdown of the intervention, iv) Conventional algorithms for removing artifacts by artificially generated magnetic fields (see, for example, [2]), as well as for other artifact removal (e.g., due to muscle twitching) ,
  • the measurement data acquisition by EEG, measurement data preprocessing and measurement data transfer in digital form along with possible artifact elimination are carried out continuously with conventional methods.
  • the measurement data are automatically processed according to the empirically validated early warning indicator used to a value of this early warning indicator.
  • the automatic intervention instructions for seizure prevention which are compatible with the seizure model used, are calculated, and their ongoing implementation via magnetic field generation (B-field generation) is carried out with the help of the transmitters.
  • the specifics of magnetic field generation (for example location, strength, direction, frequency pattern, and / or others) result from the intervention instruction.
  • the B-field changes cause intracranial induction voltages.
  • the digital control of the magnetic field generation takes place with conventional methods. Current health recommendations for extracranial generated electromagnetic radiation are known, and compliance with them is automated.
  • An early warning indicator is a quantity calculated from electromagnetic brain activity data that changes significantly before an epileptic attack. Early warning indicators are preferred for the present invention, which are changed at least a few minutes before the attack.
  • a suitable early warning indicator is the correlation of similarity indices of a predefined proportion of sensors, with falling similarity indices.
  • the similarity index is known from [1] and a number of previous publications, for example [21].
  • the average early warning time given here is 325 seconds.
  • the early warning indicator is the mutual information of similarity indices of a predefined portion of sensors, with decreasing similarity indices.
  • "Mutual information” is known as a binary logarithm of "probability of the occurrence of two random variables together divided by the product of their individual probabilities”.
  • the early warning indicator is the mutual information of similarity indices of a predefined portion of sensors, in the case of falling similarity indices, linked to activation indicators (for example, characteristic changes in body temperature when waking up, muscle movements, characteristic EEG patterns, and / or others). This minimizes the possibility of false alarms due to simultaneous changes in the patient's state of wakefulness for many sensors, with additional requirements for the device depending on the additional indicator (for example, ongoing EMG measurement).
  • activation indicators for example, characteristic changes in body temperature when waking up, muscle movements, characteristic EEG patterns, and / or others.
  • the examples given above for calculating early warning indicators do not require training phases that contain epileptic seizures.
  • the early warning indicators are calculated on the basis of a phase space representation of the normal state of the patient concerned.
  • FIGS. 6 and 7 An example of phase space embedding is given in FIGS. 6 and 7, FIG. 6 showing an EEG time series of 8 seconds for a single channel, with a sampling rate of 128 measuring points per second (x-axis time, y-axis voltage between Electrode and reference electrode in freely selected units), FIG. 7 shows a section of the time series from FIG. 6 comprising 32 measuring points starting with measuring point 128 in phase space representation (x-axis measured value at time t, y-axis measured value at time t-20).
  • the method of embedding in a phase space is described in detail in [13], for example. It is assumed here that the one-dimensional signal (as in FIG. 6) is a projection of a higher-dimensional signal which is to be restored. This higher-dimensional signal is shown in two dimensions in FIG.
  • a detection module can be specified with
  • Seizure models are used to make the intervention reliable.
  • the following models can be used as seizure models: oscillator seizure model, chaos seizure model, synergetic seizure model, stochastic oscillator seizure model, stochastic chaos seizure model, stochastic synergetic seizure model, stochastic synergetic seizure model
  • seizure models describe the parameters relevant for an epileptic seizure, which are calculated from the electromagnetic activities of neurons and / or neuron populations. These parameters are e.g. Chaoticity of the potential difference time series measured by means of an EEG electrode and its reference electrode, expressed by their maximum Lyapunov exponent [12]. Typical further parameters are critical slowdown, critical fluctuations, similarity to a normal state in the (meta) phase space, etc. These parameters are expressed by concrete numerical parameters. For example, instead of the Lyapunov exponent, the chaoticity can alternatively be represented by the embedding dimension [13], correlation dimension, Kullback-Leibler entropy, etc.
  • An oscillator seizure model is based on [3].
  • the neuron populations described here are so-called neural limit cycle oscillators, which means that they can oscillate or rest depending on the parameters.
  • the interaction of neural oscillators with each other is described with an interaction equation. This interaction presupposes the development of seizures. Preventing seizures is based on decoupling the neural oscillators.
  • phase oscillator is used synonymously with “limit cycle oscillator”.
  • limit cycle oscillator A distinction must be made here between the special case of phase oscillators (see for example [22]), in which the amplitude and phase are decoupled and only the phase of an oscillator is considered.
  • the limit cycle is bige closed curve, the phase oscillator as a circular path.
  • a corresponding seizure model is based on the increased occurrence of 1 clusters compared to other clusters.
  • a suitable interaction for the oscillator seizure model is the specific weak coupling between neural oscillators. Seizures are accompanied by an increase in the number of oscillating neural oscillators as well as increased mutual information between the oscillation frequencies of these weakly coupled neural oscillators.
  • a neural oscillator is a localized ensemble of neurons that is capable of oscillating and non-oscillating behavior. The dynamics of each neural oscillator interacting with other neural oscillators is through
  • gj is given by the Wilson-Cowan equations known from [3] for the i-th neural oscillator, hy is the strength of the connection from Zj to Zj.
  • the coupling strength epsilon is empirically between 0.04 and 0.08. If one assumes the coupling strength and connection strengths to be slowly changing compared to the time scale of a seizure, there remains primarily an intervention via the function g-. It is known from the theory of neural oscillators that they only interact in the case of oscillations, and only at commensurable oscillation frequencies.
  • neural oscillators that are adjacent and secondly that oscillate with the same and / or commensurable frequencies prior to the intervention are forced to incommensurable frequencies that are contained in their original frequencies or to nearby incommensurable frequencies (example: neighboring oscillators have the frequencies 3 Hertz and 15 Hertz , therefore force the second oscillator to the frequency 5 Hertz. Another example: both have the frequency 8 Hertz, therefore force one of them to 7 Hertz).
  • the vibrations are forced by means of magnetic fields of these frequencies at high amplitudes. Since oscillating neural oscillators and neighborhoods on the same and / or commensurable frequencies indicate the possible existence of physiological connections, the forced incommensurability, i.e. Modification of the gj, the possible and even more factual interaction between the respective zones is interrupted, which minimizes mutual information, and thus prevents the onset of seizures.
  • the complexity of the process allows the continuous real-time calculation of all required sizes.
  • step 1 Another advantageous embodiment of an instruction for the prevention of epileptic seizures that is compatible with the “seizure model with specific weak coupling between neural oscillators” is:
  • step 1 first stimulate the neural oscillators to chaotic behavior [14] (for example by time-delayed feedback with systematic error ), and then stabilize the neural oscillators in step 2 depending on the influence of the respective transmitter first orbits with incommensurable frequencies that reach them using conventional methods.
  • step 2 of this method has already proven sufficient in cell preparations to prevent the spread of seizures.
  • the algorithm used there (“OGY method”) is unsuitable for the in vivo real-time case because of its requirements for computer speed and storage capacity.
  • the chaos seizure model assumes that normal brain activity, as captured by each sensor, has a minimum of chaoticity. The seizures are accompanied by a simultaneous decrease in this chaos for all sensors. Seizures are prevented by maintaining a certain degree of chaos ([4] and [16]).
  • An intervention instruction describing the magnetic field to be generated is calculated on the basis of these models. This description is e.g. by location, strength, direction, frequency pattern, and / or other parameters of the magnetic field (B field). With this magnetic field, the electromagnetic activities of neurons and / or neuron populations are changed in a suitable manner and an impending epileptic attack is thus prevented.
  • the use of one or more seizure models reliably prevents epileptic seizures.
  • the invention is based on the knowledge that the processes leading to epileptic seizures are made quantifiable by naming suitable control parameters, so that reliable prevention is possible.
  • the preferred embodiment of the invention comprises an intervention module, which is suitable in a variety of models to prevent the attack, for example in the case of high transmitter density, the transmitters are to be divided into three classes, class 1 for chaotization, class 2 for incommensurable stabilization, - class 3 for Noise-Drowning, in such a way that in every neighborhood of each transmitter of one class there are transmitters of the other classes.
  • class 1 seizure models are satisfied, class 2 oscillator model seizures, class 3 models with stochastic components.
  • the satisfaction of synergetic models results automatically from devaluation of the master modes (by frequency shifts) while at the same time preventing the ascent from slave modes to master modes (by noise-drowning).
  • the brain activity can be measured either during or immediately after an intervention, which results in a closed control loop, since the early warning indicator and, if necessary, a further intervention instruction are calculated from the measured brain activity.
  • An advantageous embodiment of the retraction of the intervention is the sliding simultaneous retraction of all generated magnetic fields.
  • An advantageous embodiment of the retraction of the intervention is the sliding thinning of the transmitters producing magnetic fields (thinning as a spatially uniformly distributed retraction and / or switching off a percentage of all transmitters).
  • An advantageous embodiment of the retraction of the intervention is the spatially localized retraction and / or shutdown of several transmitters with gradual expansion of the area in which the retraction and / or shutdown takes place.
  • the procedure described above prevents epileptic seizures.
  • other behavioral goals preferably for healthy people, can be achieved on the basis of appropriate behavior models as well as general brain activity models.
  • the general procedure comprises the interactive determination of the non-observables of the models used for the person concerned, based on this, and based on the models the calculation of an a priori unknown intervention instruction, as well as the selective implementation of the instruction while at the same time preventing undesired propagation effects.
  • the aim of this modification is, at the request of a person, to reliably stabilize or change their behavior and / or to stabilize this change.
  • This method can be carried out with a device similar to the device described above.

Abstract

L'invention concerne un procédé et un dispositif de prévention électromagnétique commandée ou régulée, automatique et non invasive de crise épileptique in vivo en fonction de modèles de crise. Le procédé consiste tout d'abord à non seulement mesurer en continu et de manière extra-cranienne des champs électromagnétiques (en particulier des champs électromagnétiques liés à l'activité cérébrale), mais aussi à calculer en continu des indicateurs d'alerte précoces de crises à partir des données mesurées ; puis, si les indicateurs présentent des valeurs critiques, non seulement calculer en continu des interventions destinées à inhiber une crise en fonction d'un modèle de crise, mais aussi transposer en continu ces interventions par génération extra-crannienne de champs magnétiques appropriés.
PCT/EP2003/003543 2002-04-05 2003-04-04 Procede et dispositif permettant de prevenir une crise epileptique WO2003084605A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
JP2003581842A JP2005528141A (ja) 2002-04-05 2003-04-04 癲癇発作の予防のための方法及び装置
AU2003226786A AU2003226786A1 (en) 2002-04-05 2003-04-04 Method and device for the prevention of epileptic attacks
EP03745788A EP1492593A1 (fr) 2002-04-05 2003-04-04 Procede et dispositif permettant de prevenir une crise epileptique
US10/958,842 US20050107655A1 (en) 2002-04-05 2004-10-05 Method and apparatus for the prevention of epileptic seizures

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10215115A DE10215115A1 (de) 2002-04-05 2002-04-05 Verfahren und Vorrichtung zur Prävention epileptischer Anfälle
DE10215115.6 2002-04-05

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JP (1) JP2005528141A (fr)
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WO (1) WO2003084605A1 (fr)

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WO2008089741A1 (fr) * 2007-01-24 2008-07-31 Forschungszentrum Jülich GmbH Dispositif permettant de réduire le degré de synchronisation de l'activité neuronale cérébrale et bobine appropriée
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