US3495596A - Apparatus for and method of processing a bioelectrical signal - Google Patents

Apparatus for and method of processing a bioelectrical signal Download PDF

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US3495596A
US3495596A US441958A US3495596DA US3495596A US 3495596 A US3495596 A US 3495596A US 441958 A US441958 A US 441958A US 3495596D A US3495596D A US 3495596DA US 3495596 A US3495596 A US 3495596A
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signal
patient
eeg
eeg signal
carrier
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Edgar R Condict
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MEDEL CORP
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MEDEL CORP
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    • 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
    • A61N1/36021—External stimulators, e.g. with patch electrodes for treatment of pain
    • 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
    • A61B5/24—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]
    • A61B5/372—Analysis of electroencephalograms
    • 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]
    • A61B5/375—Electroencephalography [EEG] using biofeedback
    • 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
    • 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
    • A61M2021/0072—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 application of electrical currents
    • 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
    • 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
    • A61M2230/20—Blood composition characteristics

Definitions

  • This invention relates in general to the processing and use of electrical signals that are picked up from a living organism and more particularly to the employment of an electroencephalograph signal to bring about anaesthesia.
  • an electroencephalograph (hereinafter EEG) signal is processed and fed back to the patient to anaesthetize the patient.
  • EEG electroencephalograph
  • a major feature of this processing is that the EEG signal is used to modulate a radio frequency carrier.
  • the modulated carrier is fed back to the same patient from whom the EEG signal was derived in order to bring about anaesthesia.
  • the present invention in one of its aspects, proceeds on the theory that since EEG signals are generated by brain activity, or at least are concomitant therewith, the modification of such brain activity will have an effect on the nervous system. Accordingly, electrodes are placed on the skull of a patient to sense electrical impulses which are then fed back in synchronism with the generating signals. The signals picked up and processed by the electrodes are fed back by means of a feedback network so as to have the required phase relationship with the impulses internally generated by the subjects brain.
  • Applicant has found, by experimentation on small monkeys, that prolonged sleep and anaesthesia can be induced in mammals by feeding back suitably selected frequency components of EEG signals, that the effects can be maintained for as long as desired with no apparent ill-effects, and that on breaking the feedback circuit the effects can be promptly terminated.
  • the same animal has been so treated many times with no evidence of discomfort, no breakout of neurotic symptoms such as would be expected if pain had been experienced, and with no extraneous and undesirable medical symptoms developing at the time or over a long period thereafter.
  • the feedback impulses preferably should occur as modulations on a radio frequency carrier (10 kc. and higher).
  • a radio frequency carrier (10 kc. and higher).
  • feedback at relatively low levels of carrier current amplitude are successful, and small currents are conveyed to the output electrodes. Danger to the patient is thus minimized, and optimum effects obtained without destruction of pre-existing nerve paths.
  • Applicant believes the effects are due to the relative ease with which high frequencies can penetrate to cerebral pathways which control perception.
  • EKG electrocardiograph
  • patient has been employed throughout the claims and in most of the specification to indicate the organism which may be affected by the system of this invention. It shall be understood that the term patient herein is by no means limited to a human being.
  • FIG. 1 is a block diagram of the basic system of this invention employed to produce anaesthesia
  • FIG. 2 is a block diagram of a more complete system for producing electronic anaesthesia employing the basic modulation and feedback technique illustrated in FIG. 1;
  • FIG. 3 is a block diagram of a second embodiment of this invention in which the EEG signal is employed to control the magnitude of the current output by a prior art electronic anaesthetic system.
  • FIGS. 1 and 2 represent the same basic system and embodiment with FIG. 2 illustrating a large number of additional features included for the purposes of safety, monitoring and flexibility.
  • FIG. 1 in starkest terms, illustrates the basic invention. Accordingly, the same designating numerals will be used for corresponding block elements in FIGS. 1 and 2.
  • a pair of electrodes .11 are attached to the temples of a patient in order to pick up the EEG signal which is generated by the patient.
  • This signal is then amplified by an amplifier 12 so that it can be raised from a magnitude in the order of microvolts to a magnitude in the order of hundreds of millivolts.
  • the amplified EEG signal is fed as the information input to an AM modulator 20, which modulator serves to modulate a carrier signal from the oscillator 22 with the EEG signal.
  • the modulated signal is passed through a manually operable phase shifter 24 so that the operator can adjust the phase of the input to the patient to achieve maximum anaesthetic effect with minimum current input.
  • the phase shifting network 24 has been found essential, thus far, to achieving anaesthesia.
  • the appropriately phase shifted modulated signal is applied to the patient by a pair of electrodes 26. It should be noted that the output electrodes 26 may or may not be the same as the pickup electrodes 11.
  • EEG signal shall be used variously to describe both the signal that is picked up by the electrodes 11 as well as the processed signal which is supplied by the various features illustrated in FIG. 2.
  • the processed or purified EEG signal obtained by the device of this invention contains all of the signals produced by the brain or, possibly contains certain signals which are extraneous to those produced by the brain, is not to be considered a limiting factor in this invention. Applicant filters out those frequencies and spikes which appear to be dangerous to the patient and finds that the resultant signal is effective and safe. Because of the nature of what is filtered out, it would appear fairly obvious that as a co s q nce the signal obtained is in fact a much purified EEG signal. However, it seems equally certain that this processed and purified EEG signal omits certain frequencies produced by the brain. The extent of purification of modification afforded in the processed EEG signal is a matter of speculation, the resolution of which does not affect the scope of this invention.
  • the electrodes 11 are connected directly to an EEG preamplifier 12A which is nothing more than a stable low noise amplifier with a very high input impedance and a relatively low gain of about 50.
  • the output of this preamplifier 12A is then amplified by a standard amplifier 12 having a gain of approximately 1000 to provide an amplified EEG signal for processing by the remainder of this anaesthetizing circuit.
  • the amplifier 12 output is an EEG signal in the order of hundreds of millivolts.
  • the amplifier 12 output has a great deal of noise (both background noise as well as information other than the EEG signal generated by the brain).
  • This noise includes electrocardiograph signals, muscle produced signals, a possible 60 cycle signal picked up from the electronic equipment, and ambient interference which may be picked up by the electrodes 11.
  • This ambient noise may come from spark plug operation, the operation of other electrical machinery as well as the various electronic equipments which may be located in the hospital where this anaesthetic equipment is likely to be used.
  • a band pass filter 14 and lock-in amplifier 16 arrangement is employed.
  • the amplifier 12 output is divided into two branches.
  • One branch passes through a band pass filter 14 having cut-off characteristics to eliminate the very low frequency electrocardiograph and muscle produced signals on one end and the higher frequency 60 cycle (as well as other higher frequency noise) on the other end.
  • a fairly inexpensive band pass filter 14 has been employed which has a relatively fiat transmission characteristic from five to twenty cycles and is down three db at 40 cycles. As a practical matter, a five cycle lower end cut-off for the filter 14 eliminates much undersirable noise and many muscle produced signals while retaining the EEG frequencies significant for our purposes.
  • the filter 14 output is thus a somewhat purified EEG signal, which, however, carries whatever noise has been picked up or generated within the band pass range of this filter 14.
  • the output of the filter 14 provides the reference signal for the lock-in amplifier
  • the output of the amplifier 12 is fed along a second path to provide the input signal to the lock-in amplifier 16.
  • the amplifier 16 With the filtered reference signal output from the filter 14 beat against the input signal to the lock-in amplifier 16, the amplifier 16 will produce an EEG signal which is relatively free of background noise and other extraneous signals.
  • a usable lock-in amplifier is described in an article by Robert D. Moore, entitled Lock-In Amplifiers for Signals Buried in Noise, published in the June 8, 1962 edition of Electronics magazine.
  • an oscilloscope 18 at the output to the lock-in amplifier 16 is of particular value in giving an indication of the true EEG signal generated by the patient. It might also be noted that because the output of the lock-in amplifier 16 is a relatively pure EEG signal, it can be recorded to provide a reference for the patient as to his normal EEG signal.
  • a standard type of AM modulating circuit 20 is then employed to modulate this relatively pure EEG signal on the output of an oscillator 22. It is important that the frequency of the oscillator 22 be considerably higher than the frequencies which have generally been employed hitherto in electronic anaesthetization. Tests to the present time show that the frequency of the oscillator is not critical as long as it is kept at a relatively high frequency range. Frequencies anywhere within the rather broad range from 50 kc. to 15 me. have been found perfectly satisfactory. Indeed, frequencies lower than 50 kc. can be safely used but it has been found that, as the frequency is materially decreased from-50 kc., higher input currents to the patient are necessary to effect equivalent anaesthetization.
  • One of the major purposes of providing a radio frequency carrier for the EEG signal is in order to obtain the effectiveness of the EEG signal at minimum current level inputs to the patient.
  • the output of the modulating circuit 20 is fed through a phase shifter 24 before being applied to the patient in order to effect anaesthesia.
  • the phase shifter 20 is manually operated by the doctor or attendant while viewing the oscilloscope 18. For each patient and for each application of this anaesthetic technique, a particular position will be found for the phase shifter 24 that will result in a minimum EEG signal on the scope 18 thereby indicating maximum anaesthetic effect.
  • the coupling device 26 is normally a pair of electrodes which can be placed on the patients temple if general anaesthesia is to be effected. Indeed, the pickup electrodes 11 may even be employed as the output coupling device 26; providing the oscillator 22 circuit is sufiiciently well isolated from the pickup electrodes 11 circuit.
  • a high pass filter 21 prior to the output electrodes 26 in order to filter out all frequencies below some relatively safe frequency such as kc.
  • a current limiting circuit 32' is employed as a further safety measure just prior to the output electrodes 26 in order to clip any peak currents that may be put out by the power amplifier 29.
  • an oscilloscope 34 is preferably connected at the input to the patient so as to provide a Warning to the operator in case the signal being fed to the patient should become deviant or dangerous in any fashion for any reason whatsoever.
  • the current clipping circuit 32 which may be simply a Zener diode, is set at a high point of approximately ten milliamperes so as to clip any instantaneous currents over that magnitude.
  • the current input is normally at a level much under the safety limits established by the fuse 38 and clipping circuit 32.
  • the anaesthetizing system of this invention has been used hundreds of times with no ill effects on five test monkeys and two test rabbits as well as a few times on applicant himself. There are no observable ill effects or side effects and anaesthetization was instantaneous, effective and complete.
  • the band pass filter 14 has been simply described as one which eliminates all frequencies less than five cycles and all frequencies higher than forty or fifty cycles. However, it should be recognized that in the operation of this invention, the band pass filter 14 is a variable band pass filter whose upper and lower limits can be set by the operator to achieve Optimum results. It is rare that the entire range five through forty cycles is desired or needed in order to affect total anaesthesia. Since there is typically more noise than is desirable in a portion of this five to forty cycle band, the operator will typically adjust the limits of the band pass filter 14 to obtain the general anaesthesia desired with a minimum of noise being transmitted through to the modulator 20. The noise level can be monitored on the oscilloscope 18.
  • the band pass filter may be set from five to fourteen cycles (which for a filter 14, of the type involved here, that does not have sharp cut-off characteristics, means an effective pass that runs higher than fourteen cycles).
  • a compromise is struck between minmizing noise and transmitting the full scope of the EEG signal.
  • the band that is passed through the system is a frequency band wide enough to provide general anaesthesia, the purpose is served. This band that is transmitted is kept as small as possible consistent with that general purpose in order to eliminate as much noise as possible.
  • one of the major purposes of this invention is to achieve generalanaesthesia with a minimum of total current input and a minimum of extraneous signal input to the patient.
  • the filter 21 and power amplifier 29 could well be deemed a single block and labeled a tuned amplifier.
  • the amplifier 29 were tuned to the carrier frequency, the filter 21 could be eliminated.
  • phase shifter 24 which is a very important element in the anaesthetizing circuit, could be located at any positiOn subsequent to the output of the modulator. Accordingly, the various means in the claims must be understood to operate on the signal to perform the function claimed but they need not necessarily operate in the sequence claimed.
  • One of the major purposes of this invention is to effect electronic anaesthesia with a much smaller input current than has hitherto been applied to the patient thereby making electronic anaesthesia .much safer and more effective. It is presently known to apply the output of an oscillator to a subject, particularly animals, in order to induce anaesthesia. With previously known methods of electronic anaesthesia, the muscle contractions or spasms are sufiiciently serious so that a muscle relaxant such as curare has to be used.
  • FIG. 3 illustrates an improved system and technique which can be added to presently available electronic anaesthesia equipment.
  • the patient has the standard pickup electrodes 51 attached to his temples to provide an EEG signal which is amplified by a standard amplifier 52.
  • the output of the amplifier 52 is passed through a rectifier or RC circuit 54 to provide a DC control voltage.
  • the level of the DC control voltage will be a function of the average magnitude of the EEG signal so that when the patient has been anaesthetized, the level of the control voltage will decrease considerably. This DC control voltage is then employed to control the current output level of an oscillator 56.
  • the oscillator 56 output which is generally set at a given frequency, is passed through a protective filter 58 to electrodes 60 attached to the temples of the patient, thereby producing anaesthesia.
  • the output of the oscillator 56 is decreased as soon as the anaesthesia becomes effective so that the patient is not given more of a current input than the minimum necessary to provide the desired anaesthetic effect.
  • the critical elements of this invention include the concept of using the patients own EEG signal in a closed loop system to be fed back to the patient to effect anaesthesia.
  • the modulation of this EEG signal on a radio frequency carrier in order to feed the modulated carrier back to the patient is a key novel element in this invention.
  • the phase shifting device 24 is further necessary in order to assure immediate and safe anaesthetization.
  • the band pass filter 14 and lock-in amplifier 16 arrangement appears to be the least expensive and most practical means for eliminating noise and undesirable frequencies.
  • this invention is by no means limited to the particular technique shown in FIG. 2 for achieving this result. I have (for most of the experimentation) employed a spectrum analyzer in lieu of the filter 14 and amplifier 16 to provide this general (essentially filtering) function.
  • a variable band pass filter by itself if one could be obtained which would have sharp enough cut-off characteristics.
  • we wish to set the band pass filter at let us say five to fourteen cycles per second we would want a fairly sharp cut-off at five as well as at fourteen cycles.
  • Such a band pass filter with variable limits is not readily available on the market and thus the arrangement of lock-in amplifier 16 and variable band pass filter 14 shown in FIG. 2 is preferred at present.
  • This invention has been described in connection with a system where the carrier signal is amplitude modulated by the EEG signal because such a technique of modulation has been employed and found to be successful.
  • the purpose of modulation is to provide a substantially higher frequency carrier signal in order to obtain better tissue penetration and more effective anaesthesia. Accordingly, nothing herein should be construed to limit this invention to a technique of amplitude modulation. Any modulation technique may be employed which is effective to carry the EEG signal into the nervous tissue in a fashion that will permit demodulation of the signal and thus subsequent anaesthesia.
  • the nature of the modulation could be a pulse frequency modulation wherein the magnitude of the EEG signal is represented by the instantaneous pulse repetition rate of a pulse train.
  • a system for affecting the nervous system of a patient comprising:
  • pick up means adapted to be coupled to said patient to provide an electrical signal in response to a signal generated by the patient
  • modulator means to amplitude modulate said electrical signal onto said carrier signal to provide a modulated signal
  • Apparatus for feeding an electrical signal to a patient comprising:
  • pickup means adapted to be electrically coupled to said patient to provide an electrical signal in response to a signal generated from a predetermined portion of said patients body
  • a system adapted to anaesthetize a patient comprising:
  • variable phase shifting means to provide operator control over the phase between said EEG signal and said modulated signal.
  • a system for anaesthetizing a patient comprising:
  • variable phase shifting means coupled to said modulated signal to provide a phase shifted modulated signal
  • a system adapted to anaesthetize a patient comprising pickup means adapted to be coupled to said patient to provide an EEG signal,
  • a modulator coupled to said EEG signal and to said carrier signal to modulate said carrier signal with said EEG signal to provide a modulated signal
  • variable phase shifter coupled to said modulated signal to shift its phase to provide an anaesthetizing signal
  • a system adapted to anaesthetize a patient comprising a pickup electrode adapted to be coupled to said patient to provide an EEG signal,
  • a modulator coupled to said EEG signal and to said carrier signal to modulate said carrier signal with said EEG signal to provide a modulated signal
  • variable phase shifter coupled to said modulated signal to shift the phase of said modulated signal to provide an anaesthetizing signal
  • electrodes coupled to said anaesthetizing signal and adapted to be connected to said patient to impress said anaesthetizing signal onto said patient.
  • a system adapted to anaesthetize a patient comprising a pickup electrode adapted to be coupled to said patient to provide an EEG signal,
  • a modulator coupled to said EEG signal and to said carrier signal to amplitude modulate said carrier signal with said EEG signal to provide a modulated signal
  • a manually operable phase shifter coupled to said modulated signal to shift the phase of said modulated signal and thus provide an anaesthetizing signal
  • electrodes coupled to said anaesthetizing signal and adapted to be connected to said patient to impress said anaesthetizing signal onto said patient.
  • Apparatus for inducing anaesthesia in a patient comprising:
  • band pass filter means coupled to said EEG signal to provide a first filtered EEG signal
  • a lock-in amplifier having as its signal input said EEG signal and having as its reference input said first filtered EEG signal to provide a second filtered EEG signal
  • a modulator coupled to said carrier signal and to said second filtered EEG signal to amplitude modulate said carrier signal with said EEG signal to provide a modulated signal
  • a manually operable phase shifter coupled to said modulated signal to shift the phase of said modulated signal and provide an anaesthetizing signal
  • Apparatus for inducing anaesthesia in a patient comprising:
  • pickup electrodes adapted to be coupled to said patient to provide an EEG signal
  • a band pass filter coupled to said EEG signal to provide a first filtered EEG signal
  • a lock-in amplifier having as its signal input said EEG signal and having as its reference input said first filtered EEG signal to provide a second filtered EEG signal
  • a voltage clipping circuit coupled to said second filtered EEG signal to establish a maximum voltage excrusion for said second filtered EEG signal and provide a conditioned EEG signal
  • a modulator coupled to said carrier signal and to said conditioned EEG signal to amplitude modulate said carrier signal with said conditioned EEG signal to provide a modulated signal
  • a manually operable phase shifter coupled to said modulated signal to permit selectively shifting the phase of said modulated signal and provide an anaesthetizing signal
  • a high pass filter coupled to said anaesthetizing signal to provide a filtered anaesthetizing signal
  • a power amplifier coupled to said filtered anaesthetizing signal to provide an amplified anaesthetizing signal
  • a current clipping circuit coupled to said amplified anaesthetizing signal to establish a peak instantaneous current level
  • output electrodes coupled to the output of said current clipping circuit and adapted to be connected to said patient to impress said anaesthetizing signal onto the nervous system of said patient.
  • phase shifting network varying the parameters of said phase shifting network to shift the phase of said anaesthetizing signal until a minimum magnitude EEG signal is obtained
  • variable band pass filter network varying the band pass of said variable band pass filter network until a minimum frequency range for said modified EEG signal is obtained without causing an increase in the magnitude of said EEG signal.

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US441958A 1964-08-26 1965-03-23 Apparatus for and method of processing a bioelectrical signal Expired - Lifetime US3495596A (en)

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US3837331A (en) * 1972-10-24 1974-09-24 S Ross System and method for controlling the nervous system of a living organism
US3850161A (en) * 1973-04-09 1974-11-26 S Liss Method and apparatus for monitoring and counteracting excess brain electrical energy to prevent epileptic seizures and the like
US3855998A (en) * 1973-03-14 1974-12-24 Hidalgo A De Entertainment device
US3884218A (en) * 1970-09-30 1975-05-20 Monroe Ind Inc Method of inducing and maintaining various stages of sleep in the human being
US3924606A (en) * 1973-02-22 1975-12-09 Jose R Silva System and method for monitoring physiological parameters
US3951134A (en) * 1974-08-05 1976-04-20 Dorne & Margolin Inc. Apparatus and method for remotely monitoring and altering brain waves
US3967616A (en) * 1972-10-24 1976-07-06 Ross Sidney A Multichannel system for and a multifactorial method of controlling the nervous system of a living organism
US3978847A (en) * 1974-07-29 1976-09-07 Biofeedback Computers, Inc. Multiple channel phase integrating biofeedback computing method
US4031883A (en) * 1974-07-29 1977-06-28 Biofeedback Computers, Inc. Multiple channel phase integrating biofeedback computer
US4305402A (en) * 1979-06-29 1981-12-15 Katims Jefferson J Method for transcutaneous electrical stimulation
US4503863A (en) * 1979-06-29 1985-03-12 Katims Jefferson J Method and apparatus for transcutaneous electrical stimulation
US4690142A (en) * 1980-12-10 1987-09-01 Ross Sidney A Method and system for utilizing electro-neuro stimulation in a bio-feedback system
US20040073129A1 (en) * 2002-10-15 2004-04-15 Ssi Corporation EEG system for time-scaling presentations
US20110015469A1 (en) * 2008-04-09 2011-01-20 Lotus Magnus, Llc. Brain stimulation systems and methods
US20160199006A1 (en) * 2013-09-26 2016-07-14 Murata Manufacturing Co., Ltd. Biological information measurement apparatus
US20170021173A1 (en) * 2015-07-21 2017-01-26 Andreas Peneder System and method for medical devices and pain reduction

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FR2360291A1 (fr) * 1976-08-06 1978-03-03 Medicor Muevek Procede et dispositif de mesure pour reduire les effets emotionnels pendant la mesure instrumentale de donnees diagnostiques
DE3338361A1 (de) * 1983-10-22 1985-05-09 Moskovskij oblastnoj naučno-issledovatel'skij institut akušerstva i ginekologii, Moskau/Moskva Einrichtung zur zentral-elektroanalgesie
US4614193A (en) * 1984-01-09 1986-09-30 Pain Suppression Labs, Inc. Electronic glaucoma treatment apparatus and methodology
JPH0712378B2 (ja) * 1989-08-10 1995-02-15 パイオニア株式会社 脳波誘導用ゴーグルおよび脳波誘導装置
ES2464690R1 (es) * 2012-12-03 2014-12-09 María Del Pilar SÁNCHEZ JAIME Equipo de sincronismo biológico para la inducción de cambios del estado de conciencia

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US3884218A (en) * 1970-09-30 1975-05-20 Monroe Ind Inc Method of inducing and maintaining various stages of sleep in the human being
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US3837331A (en) * 1972-10-24 1974-09-24 S Ross System and method for controlling the nervous system of a living organism
US3967616A (en) * 1972-10-24 1976-07-06 Ross Sidney A Multichannel system for and a multifactorial method of controlling the nervous system of a living organism
US3924606A (en) * 1973-02-22 1975-12-09 Jose R Silva System and method for monitoring physiological parameters
US3855998A (en) * 1973-03-14 1974-12-24 Hidalgo A De Entertainment device
US3850161A (en) * 1973-04-09 1974-11-26 S Liss Method and apparatus for monitoring and counteracting excess brain electrical energy to prevent epileptic seizures and the like
US3978847A (en) * 1974-07-29 1976-09-07 Biofeedback Computers, Inc. Multiple channel phase integrating biofeedback computing method
US4031883A (en) * 1974-07-29 1977-06-28 Biofeedback Computers, Inc. Multiple channel phase integrating biofeedback computer
US3951134A (en) * 1974-08-05 1976-04-20 Dorne & Margolin Inc. Apparatus and method for remotely monitoring and altering brain waves
US4305402A (en) * 1979-06-29 1981-12-15 Katims Jefferson J Method for transcutaneous electrical stimulation
US4503863A (en) * 1979-06-29 1985-03-12 Katims Jefferson J Method and apparatus for transcutaneous electrical stimulation
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US20040073129A1 (en) * 2002-10-15 2004-04-15 Ssi Corporation EEG system for time-scaling presentations
US20110015469A1 (en) * 2008-04-09 2011-01-20 Lotus Magnus, Llc. Brain stimulation systems and methods
US9149599B2 (en) 2008-04-09 2015-10-06 Lotus Magnus, Llc Brain stimulation systems and methods
US9984584B2 (en) 2008-04-09 2018-05-29 Lotus Magnus, Llc Brain stimulation systems and methods
US10417923B2 (en) 2008-04-09 2019-09-17 Lotus Magnus, Llc Systems, apparatuses, and methods for memory recall and reactivation by targeted stimulation
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US20170021173A1 (en) * 2015-07-21 2017-01-26 Andreas Peneder System and method for medical devices and pain reduction
US20180236229A1 (en) * 2015-07-21 2018-08-23 Andreas Peneder System and method for medical devices and pain reduction

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ES316066A1 (es) 1966-03-01
BE667757A (es) 1966-02-02
ES320859A1 (es) 1966-06-16
CH467627A (de) 1969-01-31
IL24075A (en) 1969-11-30
NL6510787A (es) 1966-02-28
AT267042B (de) 1968-12-10
DE1489702A1 (de) 1969-06-04
DK118902B (da) 1970-10-19
GB1114787A (en) 1968-05-22

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