Treatment for low frequency tinnitus,earring sets for 3 piercings cc,jewellery now uk immigration - PDF Books

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A system for treating neurological conditions by low-frequency time varying electrical stimulation includes an electrical device for applying such low-frequency energy, in a range below approximately 10 Hz, to the patient's brain tissue.
FIELD OF THE INVENTIONThis invention is in the field of devices for the treatment of neurological disorders in human subjects, particularly those disorders that originate in the brain.BACKGROUND OF THE INVENTIONThe current state of the art in treating neurological disorders such as epilepsy or Parkinson's disease involves either drugs, destructive nigral lesions or the open-loop electrical stimulation of neurological tissue. Standard Edition plus low-frequency therapy device a thermal treatment to shoulder stiffness and pain treatment!
Omron [OMRON] ?????????? HV-F310 I added warm temperature treatment to a low frequency treatment device A choice of stiffness, the treatment of pain!
I warm it and massage it ???I choose the course to a symptom, and a therapy of choice is possible. Warm mode I am treated with stimulation of the warm temperature and the stimulation of the low frequency in turn. Soft mode A mind rice cake is good and unties it by soft stimulation with a few nervous feelings.
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An implantable embodiment applies direct electrical stimulation to electrodes implanted in or on the patient's brain, while a non-invasive embodiment causes a magnetic field to induce electrical currents in the patient's brain. Reimer et al., “Effects of Cerebellar Stimulation on Cobalt-Induced Epilepsy in the Cat,” Electroenceph. Goddard et al., “A Permanent Change in Brain Function Resulting from Daily Electrical Stimulation,” Experimental Neurology 25 (1969), pp. Mortimer et al., “Experimental Nondestructive Electrical Stimulation of the Brain and Spinal Cord,” J.
Bartlett et al., “Deleterious Effects of Prolonged Electrical Excitation of Striate Cortex in Macaques,” Brain Behav.
Psatta, “Control of Chronic Experimental Focal Epilepsy by Feedback Caudatum Stimulations,” Epilepsia 24 (1983), pp. Minabe et al., “Low-Frequency Kindling as a New Experimental Model of Epilepsy,” Experimental Neurology 94 (1986), pp. Agnew et al., “Considerations for Safety in the Use of Extracranial Stimulation for Motor Evoked Potentials,” Neurosurgery 20 (1987), pp. Ullal et al., “Low frequency stimulation induces an increase in after-discharge thresholds in hippocampal and amygdaloid kindling,” Epilepsy Res.
Fisher et al., “Placebo-Controlled Pilot Study of Centromedian Thalamic Stimulation in Treatment of Intractable Seizures,” Epilepsia 35(5) (1992), pp. Adamec, “Evidence that limbic neural plasticity in the right hemisphere mediates partial kindling induced lasting increases in anxiety-like behavior,” Brain Research 839 (1999), pp. Classen et al., “Epileptic seizures triggered directly by focal transcranial magnetic stimulation,” Electroencephalography and Clinical Neurophysiology 94 (1995), pp.
Migita et al., “Transcranial Magnetic Coil Stimulation of Motor Cortex in Patients with Central Pain,” Neurosurgery, vol. Wang et al., “LTD and LTP induced by transcranial magnetic stimulation in auditory cortex,” Neuroreport 7 (1996), pp. Chen et al., “Safety of different inter-train intervals for repetetive transcranial magnetic stimulation and recommendations for safe ranges of stimulation parameters,” Electroencephalography and Clinical Neurophysiology 105 (1997), pp. Wassermann, “Risk and Safety of Repetitive Transcranial Magnetic Stimulation: Report and Suggested Guidelines from the International Workshop on the Safety of Repetitive Transcranial Mag. Ettinger, et al., “Experimentation with a transcranial magnetic stimulation system for functional brain mapping,” Medical Image Analysis (1998) vol. Schulze-Bonhage et al., “Safety of single and repetitive focal transcranial magnetic stimuli as assessed by intracranial EEG recordings in patients with partial epilepsy,” J.
Maertens de Noordhout et al., “Transcranial magnetic stimulation in migraine,” Transcranial Magnetic Stimulation (EEG Suppl. Gaito et al., “Interference Effect of 3 Hz Brain Stimulation of Kindling Behavior Induced by 60 Hz Stimulation,” Epilepsia, 21 (1980), pp. Gaito, “The Effect of Variable Duration One Hertz Interference on Kindling,” Le Journal Canadien Des Sciences Neurologiques, vol. The system of claim 1 wherein the electrical stimulation signal comprises a has a fundamental frequency between approximately 4 Hz and approximately 6 Hz.
The system of claim 1, wherein one electrode of the plurality of electrodes comprises a common electrode.
The system of claim 6, wherein the electrical stimulation signal is applied for a duration, and the time-varying amplitude decreases over the duration.
The system of claim 6, wherein the electrical stimulation signal is applied for a duration, and the time-varying amplitude increases over the duration.
The method of claim 11, wherein the low-frequency stimulation signal is substantially sinusoidal. Drug therapy has been shown to have significant short and long-term side effects and is often ineffective. Visit the nearest post office with broken items, package, shipping materials and shipment invoice. If not please note so disabled and will be charged separately.To * please write the buyer reviews the must register before making a purchase in Rakuten members. With an effective tracking system and insurance program, EMS is able to offer a secure delivery worldwide.
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3,850,161, Liss describes a continuous closed-loop feedback system which will always feedback part of the brain EEG signal to separate electrodes so that if a large EEG signal occurs it will be fed back in an attempt to cancel out the original signal. This system does not take advantage of recently developed digital signal processing and microcomputer technology by which feedback signals can be activated only when a neurological event occurs, nor does it provide a practical way to recognize and intervene during early stages in the evolution of a neurological event. In addition, the Liss device is not programmable and it does not provide any capability to record EEG signals. Examples of a “neurological event” are the occurrence of an epileptic seizure, a tremor or the occurrence of a migraine aura or migraine headache. A “neurological event” is defined herein as either the precursor of an event such as an epileptic seizure, or the event itself.
This concept of detecting an electrical precursor that is a first type of neurological event that occurs some time before the “real” event (i.e.
It has been shown that both epileptic seizures and Parkinson's tremors have precursors that occur before and can be used to predict the onset of the clinical symptom. It is also very likely that other neurological events such as migraine headaches and depression would have anomalous electrical activity predictive of the onset of clinical symptoms. Methods for prediction of epileptic seizures have been published by Elger and Lehnertz (in Elger, C. 4,373,527 describes a programmable medication infusion system but does not anticipate its use in response to a detected neurological event.More recently, a device has been approved for human use to stimulate the vagus nerve in a continuous fashion with the objective of decreasing the rate of epileptic seizures.

Clinical reports on such devices indicate only a modest degree of success in that only 50% of the patients experience a greater than 20% reduction in the rate of epileptic seizures.
Another device that has been recently introduced into clinical practice utilizes intermittent or continuous stimulation of the thalamus for the treatment of involuntary motion disorders such as Parkinson's syndrome.
Neither of these two open-loop devices described above is highly effective for the treatment of a neurological disorder such as epilepsy, and neither anticipates the use of decision making in order to optimize a response to terminate the precursor of a neurological event or the neurological event itself; nor does either device allow for the recording of EEG signals.
6,016,449, which is incorporated herein by reference, teaches a fully implantable neurostimulator capable of responsive treatment of neurological disorders. However, Fischell does not discuss in detail the advantageous use of low frequency stimulation as a means of inhibiting epileptiform activity.It is well known that slow wave potentials in the brain are often inhibitory in nature yet all known stimulation attempts to treat epilepsy in humans have used relatively high frequency stimulation, in most cases greater than 20 Hz. These higher frequencies, while effective for a brain mapping type procedure, have significant potential to induce epileptogenic activity. 13, 2000, states that while “rapid repetitive transcranial magnetic stimulation (rTMS), at frequencies of 5 Hz and higher, will transiently enhance motor excitability . Observations on the origins of phase III delta energy and the mechanism of action of ECT,” Clin. The article also states that stimulation of the thalamus, mesencephalic reticular formation or hypothalamus was not effective. A purpose of the present invention is to overcome the shortcomings of all known devices for the treatment of such disorders. Specifically, the present invention utilizes slow wave potentials (low frequency stimulation in a range of approximately 1 to 10 Hz) to prevent or abort a neurological event.One embodiment of the present invention envisions a multiplicity of brain electrodes placed either within the brain, on the surface of the brain itself, or on the dura mater that surrounds the brain.
Some or all of these brain electrodes may be used to directly detect an abnormal neurological event such as an epileptic seizure, or they may be used to detect a pattern of electrical activity that precedes or accompanies an abnormal neurological event. A stimulation signal can also be applied to any one, several, or all elements of such an electrode array. The is stimulation signals sent to each electrode may be identical or they may be programmed to differ in amplitude, frequency, waveform, phase and time duration. Thus, the present invention envisions enhancement of detection by the use of the spatial domain as it applies to the positioning of detection and treatment electrodes.A specific capability of this system is to provide electrical stimulation to a specific portion of the brain as the means of stopping a neurological event. It is believed that the earliest possible detection of a seizure and treatment of aberrant electrical activity from an epileptic focus has the highest probability of aborting the occurrence of a full seizure. It is envisioned that either through specific placement of treatment electrodes or by adjusting the phase of signals applied to an array of electrodes, stimulation can be directed to the location(s) within the brain that offer the highest probability of stopping the seizure.
Such placement will either have the device located between the scalp and the cranium or the within a hole in the cranium. The battery that provides power for the system and an electronics module are both contained within a metal shell that lies, in one embodiment, under the patient's scalp. The metal shell, which contains the electronics module and the battery collectively, forms the control module.All electrodes connect by way of electrically conducting wires to electrical terminals that are formed into the metal shell.
By placing the entire system within the cranium, (as opposed to having some wires extending into or through the patient's neck to a control module in the chest) the probability of wire breakage due to repeated wire bending is significantly reduced.
However, the present invention also envisions the placement in the chest or abdomen of a control module if a large battery or a large volume electronics module dictates such a large size for the control module that it cannot be conveniently placed within the cranium.
Such a thoracic or abdominal placement of a control module would typically require wires to be run through the patient's neck.The present invention also envisions the utilization of an intracranial system for the treatment of certain diseases without placing wires through the neck.
In one embodiment of the invention, the stimulation waveform is substantially sinusoidal and has minimal higher-order harmonics, and hence little energy above the fundamental frequency. In an alternative embodiment, the low frequency stimulation comprises a sequence of short duration biphasic pulses having a repetition rate of less than about ten pulses per second (10 Hz). Such stimulation could be applied to the caudate nucleus or other structures of the brain, including the hippocampus.
As patients suffering from Parkinson's have an extremely low incidence of epilepsy and one manifestation of Parkinson's is characterized by a 5 Hz electrical oscillation that begins in the Thalamus, it is conceived that low frequency stimulation of the Thalamus could, in fact, be inhibitory to epileptiform activity. Such stimulation could be responsive to the detection of a precursor to a clinical seizure or the epileptiform activity from the seizure itself.
Alternately, periodic slow wave stimulation applied without detection could prevent the brain from generating seizure activity. Although epilepsy is currently believed to be the most applicable use of such slow wave stimulation, it could also be successful for migraines, pain, tremor, Parkinson's, depression or other neurological disorders.It is also envisioned that while the standard treatment would have a constant amplitude for the duration of the low frequency stimulation, it may be advantageous to have the amplitude begin high and decrease over the duration, begin low and increase over the duration, or vary according to any desired treatment plan. The typical duration of low frequency stimulation that would be used to stop a neurological event would be between 100 ms and 10 seconds.Another embodiment of the present invention that would be significantly less invasive involves the use of Transcranial Magnetic Stimulation (TMS) from an external coil TMS stimulator. Such a device could be incorporated into a bicycle type helmet and could be used at the time a pre-event aura is sensed by the patient. Alternately, such an external system could be used in a repetitive or continuous mode for patients with serious disorders who often wear protective helmets. A TMS device could be extremely effective if it is pulsed on and off at frequencies below 10 Hz.Thus it is an object of this invention to provide appropriate slow wave stimulation of the human brain in response to a detected neurological event in order to cause the cessation of that neurological event. 1 is a top view of a human head showing the configuration of an implantable system for the treatment of neurological disorders, as it would be situated in the human skull.FIG. 3 is a cross section of an embodiment of the present invention showing a magnetic depolarizer system within a helmet on the head of a patient.FIG. 5 is a simplified circuit diagram of the main components of a magnetic depolarizer system.DETAILED DESCRIPTION OF THE DRAWINGSFIG.
It is envisioned that the control module 20 is permanently implanted into the top of the patient's skull in a location where the skull is fairly thick. It is also envisioned that the control module 20 could be located in the trunk of the patient's body like a heart pacemaker with the connecting wires being run through the patient's neck, under the patient's skin or otherwise. 1 through 5, inclusive, lines connecting boxes on block diagrams or on software flow charts will each be labeled with an element number. A physical connection, namely a wire or group of wires (data bus) over which analog or digital signals may be sent.2. Data streams include messages, analog or digital signals, commands, EEG information, and software downloads to change system operation and parameters.3.
In one embodiment of the invention, it is also envisioned to use the case of the control module 20 of FIG.
Although the electrodes 15A through 15N and 16 shown here are connected to both the event detection sub-system 30 and the stimulation sub-system 40, it should be apparent that a separate set of electrodes and associated wires could be used with each sub-system. This would be accomplished by appropriate switching circuitry in the stimulation sub-system 40.The event detection sub-system 30 receives the EEG signals 21A through 21N (referenced to a system ground 19 connected to the wire 18 from the common electrode 16) and processes them to identify neurological events such as an epileptic seizure or its precursor. A central processing its system 50 with a central processor 51 and memory 55 acts to control and coordinate all functions of the implantable system 10. A first interconnection 52 is used to transmit programming parameters and instructions to the event detection sub-system 30 from the central processing system 50.
A second interconnection 53 is used to transmit signals to the central processing system 50 identifying the detection of a neurological event by the event detection sub-system 30.
It is anticipated that, if appropriate, electrical signals 412A to 412N, inclusive, are transmitted to certain locations in or near the brain, thereby aborting the normal progression of an epileptic seizure. It may also be necessary for the stimulation sub-system 40 to temporarily disable the event detection sub-system 30 via a fourth interconnection 29 when stimulation is imminent so that the stimulation signals are not inadvertently interpreted as a neurological event by the event detection sub-system 30.The stimulation sub-system 40 may also be engaged to perform continuous or periodic stimulation to the brain electrodes 15A through 15N, inclusive. In one embodiment of the by invention, electrical stimulation from the stimulation sub-system 40 can include any of a wide range of frequencies from approximately 2 Hz to approximately 200 Hz. Details of a signal generator capable of generating waveforms over such a frequency range are well known in the art of electronics design.

In connection with the invention, it is, however, highly desirable to use stimulation at frequencies below 10 Hz. In particular, 5 Hz stimulation has been shown to be inhibitory to ictal spikes in cat brains, and it is believed to be similarly effective in human patients. Power supplies for comparable implantable devices such as heart pacemakers and heart defibrillators are well known in the art of implantable electronic devices.
Such a power supply typically utilizes a primary (non-rechargeable) storage battery with an associated d-c to d-c converter to obtain any voltages required for the implantable system 10. However, it should be understood that in an alternative embodiment of the invention, the power supply could use a rechargeable battery that is charged by means of a coil of wire in the control module 20 that receives energy by magnetic induction from an external coil that is placed outside the patient but in close proximity to the control module 20.
The implanted coil of wire could also be located remotely from control module 20 but joined to it by electrical wires. Furthermore, the same pair of coils of wire could be used to provide power to the implanted system 10 when it is desired to read out stored telemetry or reprogram some portion of the implanted system 10.The central processing system 50 is connected to a data communication sub-system 60, thereby allowing data stored in the memory 55 to be retrieved by the patient's physician via a wireless communication link 72. An external data interface 70 can be directly connected to the physician's workstation 80 via a traditional serial data connection 74 (such as an RS-232 interface).
Alternately, the serial connection may be made trans-telephonically, via modems 85 and 750 and a phone line 75 from the patient's home to the physician's workstation 80. Software in the computer section of the physician's workstation 80 allows the physician to read out a history of events detected by the implantable system 10, including EEG information before, during and after each event, as well as specific information relating to the detection of the event, such as the time evolving energy spectrum of the patient's EEG. In a preferred embodiment of the invention, the physician's workstation 80 also allows the physician to specify or alter any programmable parameters of the implantable system 10.As shown in FIGS.
1 and 2, a buzzer 95 connected to the central processor 51 via a link 92 can be used to notify the patient that a neurological event has occurred, the implanted system 10 is about to deliver stimulation, or that the implanted system 10 is not functioning properly. In alternative embodiments, the buzzer could provide a mechanical vibration (typically an acoustic signal) or an electrical stimulation “tickle,” either of which could be perceived by the patient. By placing the buzzer 95 near the ear and on the top of, below, or within a burr hole in the cranium, an acoustic signal emitted by the buzzer 95 would be transmitted via bone conduction and detectable by the patient's ear. This sound by itself can be an automatic means for stopping an epileptic seizure.A real time clock 91 is used for timing and synchronizing various portions of the implanted system 10 and also to enable the system to provide the exact date and time corresponding to each neurological event that is detected by the implantable system 10 and recorded in the memory 55. 2 for detecting and treating a neurological event such as an epileptic seizure would typically be as follows:1. When an event is detected, the event detection sub-system 30 notifies the central processor 51 via the second interconnection 53 that an event has occurred.3.
The central processor 51 then triggers the stimulation sub-system 40 via the third interconnection 54 to electrically stimulate the patient's brain with low frequency electrical signals in order to stop the neurological event, using any one, several or all of the electrodes 15A through 15N.4. The stimulation sub-system 40 also sends a signal via the fourth interconnection 29 to the event detection sub-system 30 to disable event detection during stimulation to avoid an undesired input into the event detection sub-system 30.5.
The central processor system 50 will store EEG signals and event related data received from the event detection sub-system 30 via the second interconnection 53 over a time from X minutes before the event to Y minutes after the event for later analysis by the patient's physician. The central processor 51 may generate a “buzz” to notify the patient that an event has occurred by sending a signal via the link 92 to the buzzer 95.An alternative embodiment of the invention is shown in FIG. 3, which illustrates the head of a patient showing a cross section of a non-invasive transcranial magnetic depolarizer system 100 as it would be contained within a helmet 111 of the type used by bicycle riders. The magnetic depolarizer system 100 consists of a magnetic depolarizer coil assembly 112, a battery 114, electronic circuitry 115, a recharging receptacle 116 and interconnecting wires 117. The magnetic depolarizer system 100 is contained within the helmet 111 by means of an elastic support 113 that passes between a front support 111A and a rear support 111B. The purpose of the elastic support 113 is to keep the magnetic depolarizer coil 112 in comparatively tight contact with the patient's head and at a specific location relative to the patient's cerebral cortex.FIG. The magnetic depolarizer coil assembly 112 consists of a first coil 121 placed into a figure-eight configuration with a second coil 122.
The two coils 121 and 122 are electrically connected in series in such a way as to create north magnetic poles 121A and 122A in essentially opposite directions when electric current is flowing through the coils 121 and 122. This orientation of coils 121 and 122 can produce a comparatively strong magnetic field onto the cortex of the brain for a distance of a few centimeters beneath the cranium. If the magnetic field changes rapidly in time, it produces an electric current in the brain that can cause excited neurons to be depolarized.
In an embodiment of the invention, the intensity of the magnetic field at the surface of the brain should be between 0.1 and 10 Tesla. 3 pulsed at a slow rate such as 1 or 2 Hz as an external means for treating a neurological disorder; preferably, this frequency is set and evaluated by the patient's physician. Such a device could be worn all the time for chronic epileptics where periodic slow stimulation would act to keep the focal region in a depressed condition, thus preventing a hyperexcited state associated with an epileptic seizure. 4B is a top view of the magnetic depolarizer coil assembly 112 showing as dotted lines the outline of the coils 121 and 122. 4A and 4B, it is shown that the coils 121 and 122 could be encapsulated into a plastic housing 125.
4A shows a magnetic core 123 in the coil 121 and a separate magnetic core 124 in the coil 122. These cores 123 and 124 are not required for the device to perform its intended purpose of generating a depolarizing electric current within the cerebral cortex, but their presence facilitates the generation of a high-intensity magnetic field in the brain at a lower level of electric current in the coils 121 and 122.
To be effective at the high frequency of the magnetic pulses that are used to stimulate the cortex, the cores 123 and 124 would typically be formed from powdered iron or equivalent ferromagnetic material that has low eddy current and hysteresis losses.Although FIGS.
4A and 4B show a race-track, figure eight type of design for the magnetic depolarizer coil assembly 112, it should be understood that a simple cylindrical coil (and other shaped coils as well) with or without a ferromagnetic core could be used generate the desired time-varying magnetic field.FIG. When the patient is experiencing an aura of a migraine headache or other symptoms of a neurological disorder, he or she can throw the ON-OFF switch 129 to the ON position. That would cause the d-c to d-c converter 130 to activate and generate a high voltage for rapidly charging the capacitor 126. When the control circuitry 128 senses that the appropriate voltage has been reached, it moves the switch 127 from position A to position B thus discharging the capacitor 126 through the coils 121 and 122 of the magnetic depolarizer 112. As previously described, the coils 121 and 122 could have air cores or they could use magnetically permeable cores 123 and 124. The control circuitry 128 can be used to set the repetition rate for causing magnetic pulses to be delivered. For example, a pulse from the capacitor might last for 70 microseconds and could be repeated at the slow frequency rates between approximately 0.1 and 10 Hz. A frequency of 1 Hz has been shown to be effective in depolarizing brain neurons and may be ideal for some patients. It should be recognized that the carrier frequency given here is considered representative of a beneficial and advantageous carrier signal, and that various other carrier frequencies and modulation schemes are possible.
Various waveforms are also possible for both the TMS waveform and the carrier waveform, including the substantially sinusoidal wave described above. Circuits capable of generating such stimulus signals are well known to practitioners skilled in the art of electronic circuit design.Although FIGS.
3 and 5 show a battery operated magnetic depolarizer system 100, the system 100 could be operated by plugging into a receptacle at (typically) 115 or 230 volts a-c.
Such a system might or might not use a battery as part of its circuitry.Additional objects and advantages of the present invention will become apparent to those skilled in the art to which this invention relates from the subsequent description of the preferred embodiments and the appended claims, taken in conjunction with the accompanying drawings.

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