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WO2023220573A2 - Système et procédé de surveillance et de stimulation cérébrale ambulatoire - Google Patents

Système et procédé de surveillance et de stimulation cérébrale ambulatoire Download PDF

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Publication number
WO2023220573A2
WO2023220573A2 PCT/US2023/066751 US2023066751W WO2023220573A2 WO 2023220573 A2 WO2023220573 A2 WO 2023220573A2 US 2023066751 W US2023066751 W US 2023066751W WO 2023220573 A2 WO2023220573 A2 WO 2023220573A2
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WO
WIPO (PCT)
Prior art keywords
electrode
seeg
coupling component
brain
patient
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Ceased
Application number
PCT/US2023/066751
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English (en)
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WO2023220573A3 (fr
Inventor
Ross Tsukashima
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Sensoria Therapeutics Inc
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Sensoria Therapeutics Inc
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Publication date
Priority claimed from US17/741,243 external-priority patent/US20230363691A1/en
Priority claimed from US17/741,205 external-priority patent/US20230364422A1/en
Application filed by Sensoria Therapeutics Inc filed Critical Sensoria Therapeutics Inc
Publication of WO2023220573A2 publication Critical patent/WO2023220573A2/fr
Publication of WO2023220573A3 publication Critical patent/WO2023220573A3/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
    • A61B5/293—Invasive
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/07—Endoradiosondes
    • A61B5/076—Permanent implantation
    • 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
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/271—Arrangements of electrodes with cords, cables or leads, e.g. single leads or patient cord assemblies
    • 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]
    • A61B5/384—Recording apparatus or displays specially adapted therefor
    • 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
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/0526—Head electrodes
    • A61N1/0529—Electrodes for brain stimulation
    • A61N1/0534—Electrodes for deep brain stimulation
    • 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
    • A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
    • A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
    • A61N1/36064—Epilepsy
    • 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
    • A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
    • A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
    • A61N1/36067—Movement disorders, e.g. tremor or Parkinson disease
    • 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
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/37211—Means for communicating with stimulators
    • A61N1/37217—Means for communicating with stimulators characterised by the communication link, e.g. acoustic or tactile
    • 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
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/378—Electrical supply
    • A61N1/3787—Electrical supply from an external energy source
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0204—Operational features of power management
    • A61B2560/0214—Operational features of power management of power generation or supply
    • A61B2560/0219—Operational features of power management of power generation or supply of externally powered implanted units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6864—Burr holes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/06—Radiation therapy using light
    • A61N5/0613—Apparatus adapted for a specific treatment
    • A61N5/0622—Optical stimulation for exciting neural tissue

Definitions

  • the inventions described below relate to the field of brain monitoring systems for diagnosis and prognosis of epilepsy and other motor disorders .
  • Stereo-electro-encephalography is a method for determining whether a patient with epilepsy which has not responded to medication might have "focal epilepsy" which might be treated with brain surgery.
  • Stereo-elector-encephalography requires short term implantation of many electrodes into the brain, in many parts of the brain, and recording of electrical activity detected by the brain in hopes of identifying an area of the brain which is the focus of the epilepsy, which is referred to as an "epileptogenic" area.
  • an epileptogenic area is identified after analysis of electrical activity, this indicates that the surgical resection of the epileptogenic area might result in alleviation of epileptic seizures. For example, if analysis of the electrical signals from the electrodes indicates that activity in the temporal lobe is the origin of seizures, removal of the temporal lobe may eliminate seizures altogether .
  • stereo-electro-encephalography is accomplished by implanting numerous electrodes deep in the brain , with electrical leads extending through the brain , through burr-holes in the skull , and then a bundle of the leads extend several feet to a console or EEG monitoring system, such as a Kohden Neurofax EEG-1200 console , which records data from the leads .
  • the leads have to remain in place for several days ( ten to thirty days , typically ) to detect a suf ficient number of seizures and collect enough data to confirm that an epileptogenic focus has been identified with enough certainty to justify removal or ablation of a part of the patient ' s brain .
  • the electrodes are removed . If analysis of the collected electro-encephalography data leads to a conclusion that resection of the "epileptogenic" area will likely lead to cessation of seizures , resection can be performed at any time after removal of the electrodes .
  • DBS Deep brain stimulation
  • Typical protocols use multiple sensor probes and stimulation probes attached to wiring that is connected to an implantable pulse generator .
  • the sensor probes are implanted in the brain
  • the pulse generator is implanted under the skin of the chest or abdomen , and the two are connected by an insulated wire that runs below the skin , from the head, down the side of the neck, behind the ear , to the pulse generator .
  • the current method entails surgical implantation of wires and components under the skin of the patient , in addition to the surgical implantation of probes and leads in the brain of the patient . Summary
  • the devices and methods described below provide for more convenient stereo-electro-encephalography, which may allow the patient to move freely during the days-long monitoring period .
  • the system and method also entails a lower risk of infection , more discrete usage of the system, and a lower risk of lead breakage and resultant loss of signal , and lower risk of interference because the lead length is much shorter .
  • the system includes a number of SEEG electrodes , which are configured for implantation and explantation in the brain , and configured for use in encephalography .
  • each SEEG electrode is wirelessly connected to an EEG console , through a subcutaneous electrode which is connected to the SEEG electrode through a conductor .
  • the subcutaneous electrode is in turn wirelessly connected to a supracutaneous appliance operable to obtain SEEG signals , generated by the SEEG electrode , through the subcutaneous electrode .
  • Other wireless communication schemes may also be used .
  • the method of use entails implantation of the SEEG electrodes deep in the brain and implantation of the subcutaneous electrodes under the scalp (with the conductor running through the brain ) .
  • the patient need not be physically connected to a console or control system, and may be ambulatory for the SEEG protocol period .
  • the devices and methods described below also provide for improved treatment of movement disorders using sensor probes and stimulation probes operated by an external control system .
  • the system includes a control system, a power source , and power coupling that can be placed on the scalp of a patient , an intracranial electrode , surface patch electrode which can be placed superficially on , or subcutaneously under , the scalp of a patient , a second, subcutaneous electrode configured for placement under the scalp of the patient , an implantable probe with an electrode array or other stimulation mechanism configured for implantation in the brain , and an electrical wire connecting the second electrode and the implant , operable as a conductor for delivery of power to the implant and delivery of sensor signals from the implant .
  • the system includes a control system operable to deliver power to the implant through a circuit comprising the power coupling, the intracranial electrode , brain tissue of the patient to the probe (with no wired connection between the intracranial electrode and the probe ) , a wired connection to the subcutaneous electrode and through the subcutaneous scalp tissue to the patch electrode and hence to the power coupling .
  • the system may be optionally operable to receive sensor signals from the implant , through the same circuit pathway, and provide bi-directional communications between the control system and the implantable probe through the inductive coupling .
  • the system is operable to deliver therapeutic and/or diagnostic stimulation to the brain , and also to obtain diagnostic information from the brain .
  • Figure 1 illustrates a system for treatment of movement disorders using sensor probes .
  • Figure 2 illustrates the SEEG electrode , subcutaneous electrode , and patch electrode of Figure 1 .
  • Figure 3 illustrates a system similar to the system of Figure 1 with the addition of an NFC/RFID transponder .
  • Figure 4 depicts the system similar to the system of Figure 1 with the addition of a number of NFC/RFID transponders .
  • Figure 5 illustrates an assembly of a SEEG electrode , inductive power supply and NFC/RFID transponder .
  • Figure 6 illustrates a SEEG system similar to the system shown in Figure 4 , in which the SEEG electrodes are powered with batteries .
  • Figure 7 illustrates an assembly of a SEEG electrode , battery power supply, and NFC/RFID transponder .
  • Figure 8 illustrates a SEEG system in which the SEEG electrodes are packaged along with the NFC/RFID components of Figures 5 or 7 in a single housing .
  • Figure 9 illustrates a combined assembly of the NFC/RFID components of Figure 5 or 7 in a single housing .
  • Figure 10 illustrates a system for diagnosis and treatment of movement disorders using sensor probes and stimulation probes operated by an external control system .
  • Figure 11 illustrates the probe and subcutaneous electrode .
  • Figure 1 illustrates a system for monitoring and diagnosis of movement disorders using sensor probes installed in the brain .
  • a patient 1 with a movement disorder and requiring diagnosis of a condition of the brain 2 is illustrated .
  • Figure 1 shows the placement of a plurality of probes 3 .
  • the probes are preferably SEEG electrodes , and may be SEEG "depth electrodes" specifically suited for SEEG protocols and temporary implantation and short-term explantation ( but may be other sensor probes and may have stimulation capability ) .
  • the sensor probes can be inserted entirely within the brain , at various locations in the brain.
  • Figure 1 also illustrates the scalp 4, the skull 5 which is beneath the scalp, the dura 6 which is beneath the skull and the cerebral cortex 7 which is beneath the dura .
  • the probes 3 of Figure 1 are attached to subcutaneous electrodes 8, which are implanted in a subcutaneous location (under the skin, superficial to the skull) under the scalp, through conductors 9, and together these components comprise a SEEG electrode assembly.
  • the probes have been inserted into the brain of the patient through openings (typically, burr-holes) in the skull, and driven through the brain and deposited at a location determined by a surgeon and known to effect target disorders, or known to produce signals indicative of target disorders, such as epilepsy.
  • the leads may be secured in the burr hole with lead anchors to prevent migration during the SEEG monitoring protocol period.
  • the system can be configured as described in our co-pending U.S. Patent Application 17/741,205, filed May 10, 2022, entitled Deep Brain Stimulation System with Wireless Power, the entirety of which is hereby incorporated by reference, and the electrodes may be powered and signals indicative of brain activity (EEG's, for example) obtained through the system disclosed therein.
  • EEG's brain activity
  • the patch electrode 10 is disposed on the scalp, supracutaneously on the scalp, or subcutaneously under the scalp.
  • the patch electrode is, preferably, located such that it is not in direct physical contact with the electrodes 8, and is spaced from the electrodes 8.
  • the patch electrode 10 is connected to the secondary (remote) coupling component 11S of a coupling assembly 11, and the primary (base) coupling component IIP is connected to the power supply and control system 12.
  • a conductor 13 extends from the secondary (remote) coupling component 11S, through a burr-hole and into the brain, and may be an insulated wire and include an electrode 14 at its distal end (a conductive wire, insulated or bare, will suffice) .
  • An additional conductor connects the secondary (remote) coupling component 11S to the patch electrode 10.
  • the control system is configured to provide power to the probes, for stimulation of brain tissue proximate the probes, and receive sensor data from the probe.
  • the control system or console used to control the system and/or receive and store EEG data from the SEEG electrodes may be implemented on a dedicated console such as the Kohden Neurofax EEG-1200 console (without all the wires) , and EEG monitoring system, a general purpose computer, or a mobile phone or tablet.
  • the coupling assembly is an inductive coupling assembly, comprising a pair of coils.
  • the secondary (remote) coupling component 11S may, like the patch electrode, also be installed on the scalp, supracutaneously , or subcutaneously under the scalp.
  • the primary (base) coupling component IIP may be placed in proximity to the secondary coupling using a magnetic attachment or other releasable attachment means (a snap lock fitting, secured to a headband, glued to the overlying skin with a weak adhesive) or non- releasable means (stitched to the scalp, nailed or screwed to the skull, or other means not considered “releasable” attachment means which require tools for removal) .
  • the control system 12 is operable to generate power and transmit power through the inductive coupling to the electrodes and may be further programmed to analyze the sensor data and modify control signals to the probes to control the stimulation provided by the probes in response to the sensor data .
  • the power supply and control system 12 may be disposed in an appliance , which may be configured as headwear ( disguised as a hat , head band, or wig ) .
  • the power supply may be connected to the SEEG electrodes through the inductive coupling, and may be connected substantially continuously during the SEEG monitoring protocol period of several days to several weeks .
  • the power supply is preferably not implanted subcutaneously on the patient ' s chest of abdomen , as is the practice with pulse generators used with DBS systems .
  • Figure 2 illustrates the SEEG electrode 3 , subcutaneous electrode 8 , and patch electrode 10 of Figure 1 and the circuit for obtaining EEG signals from the probe .
  • the probe 3 includes several sensor/stimulation electrodes 21 , and an LED assembly 22 which includes an LED 23 , and a power contact 24 for providing power to the electrodes 21 and the LED 23 or providing a ground path/return path for the LED .
  • the sensor/stimulation electrodes are connected to the subcutaneous electrode 8 , and may be operated, in conjunction with the subcutaneous electrode 8 to apply electrical stimulation to brain tissue or sense electrical signals of the brain , or both .
  • Figure 2 also shows the conductor 9 and subcutaneous electrode 8 .
  • the subcutaneous electrode 8 which is preferably configured for implantation under the scalp ( in the subcutaneous tissue 25 of the scalp (which may include connective tissue , epicranial apaneurosis , areolar connective tissue , and periosteum) ) , may consist of a bare conductive plate (metal such as stainless steel , or carbon fiber or glassy/pyrolytic carbon ) , but may also consist of a conductive plate covered in a thin layer of insulation .
  • the subcutaneous electrode 8 may also comprise a near field communication coil (an NFC/RFID tag ) configured to communicate with the control system through a corresponding emitter and NFC/RFID controller of the control system (which may be housed proximate the patch electrode or housed in a separate appliance ) .
  • the conductor 9 also functions as a tether for retrieval of the probe from the brain .
  • the power contact 24 on the probe tip may be bare , uncoated metal or other conductive material , or may be coated with a non-insulating coating with or without biologic ef fect , or covered in an insulating layer and work in conjunction with an insulated subcutaneous electrode 8 for capacitive coupling of both components of the probe to the conductor 13 of the secondary coil 11S .
  • the conductors 9 may be f loppy, having little or no columnar strength , with a small diameter merely suf ficient to conduct signals to the subcutaneous electrodes .
  • the conductors may be characterized by column strength insuf ficient to support pushing the probe through the brain , and the conductors may or may not include a lumen which accommodates a stylet which is used in some depth electrodes to stif fen the length of the SEEG electrode in order to push it through the brain .
  • the system may be used in a method in which a surgeon implants a number of SEEG electrodes 3 ( about 20 ) in the brain of a patient , in areas of the brain which may be the focus or origin of brain activity associated with a movement disorder , and places the subcutaneous electrodes under the scalp of the patient , in the subcutaneous tissue 25 of the scalp (which may include connective tissue , epicranial apaneurosis , areolar connective tissue , and periosteum) , and implanting the patch electrode also subcutaneously, and implanting the secondary ( remote ) coupling component 11S pericutaneously ( preferably subcutaneously, or perhaps supracutaneously ) , and installing the tip of the conductor 13 in the brain .
  • a surgeon implants a number of SEEG electrodes 3 ( about 20 ) in the brain of a patient , in areas of the brain which may be the focus or origin of brain activity associated with a movement disorder , and places the subcutaneous electrodes under the scalp of the patient , in the subcutaneous tissue 25 of the
  • the surgeon or the patient may place the primary ( base ) coupling component I IP proximate the secondary ( remote ) coupling component 11S .
  • the control system may be operated to collect EEG signals from the various implanted SEEG electrodes .
  • the coupling may be maintained for the entire monitoring period, for substantially the entire period (excepting brief periods ) .
  • EEG data may be collected continuously while the coupling is maintained .
  • FIG. 3 An embodiment which includes memory is depicted in Figure 3 , which depicts the system similar to the system of Figure 1 with the addition of an NFC/RFID transponder .
  • the system of Figure 1 may be modified by adding memory for storage of data, so that the system may be operated continuously to collect EEG data but need not be continuously connected to the control system .
  • the system may include a single NFC/RFID transponder assembly 31 ( a tag ) which may be located in any convenient location but is shown in a pericutaneous location ( subcutaneous or supracutaneous proximate the secondary ( remote ) coupling component 11S ) , and may be formed integrally with the secondary ( remote ) coupling component 11S .
  • This NFC/RFID transponder 31 is electrically connected to the patch electrode for collecting EEG data, and may be electrically connected to the secondary ( remote ) coupling component 11S for power .
  • the NFC/RFID transponder 31 includes memory for storing EEG data from the several SEEG electrodes 8 .
  • the SEEG electrodes 8 and NFC/RFID transponder 31 may be continuously powered through the inductive coupling, through a power source disposed on the scalp or more remotely ( outside the brain ) .
  • the system includes an NFC/RFID reader 32 , which is operable to occasionally interrogate the NFC/RFID transponders 31 and obtain EEG data from the SEEG electrodes which has been stored in memory on the NFC/RFID transponder 31 .
  • the NFC/RFID reader 32 may store the data and/or transmit it to a control system for analysis of the EEG by a neurologist .
  • FIG. 4 Another variation of the system which includes memory is depicted in Figure 4 , which depicts the system similar to the system of Figure 1 with the addition of a number of NFC/RFID transponders .
  • Each subcutaneous electrode 8 may be replaced with an NFC/RFID transponder 31 , with memory for storing historical EEG data .
  • the NFC or RFID transponders 31 in this system are preferably powered in the same manner as the SEEG sensors , with power supplied from a power supply 33 through the inductive coupling 11 .
  • the NFC or RFID transponders 31 may instead include a small power source , or a radio chip attached to an antenna for wireless power needed to operate the SEEG electrodes and store EEG data .
  • This system includes an NFC/RFID reader 32 ( several readers , or a single reader ) which are operable to occasionally interrogate the NFC/RFID transponders
  • the 32 may store the data and/or transmit it to a control system for analysis of the EEG by a neurologist .
  • Figure 5 illustrates a transponder and SEEG electrode assembly 34 which includes the NFC/RFID transponder 31 , a SEEG electrode 3 and NFC/RFID transponder microchip 35 , NFC/RFID antenna 36 and memory 37 .
  • a battery 38 may be included .
  • These components may be mounted on circuit board 39 and housed in a housing 40 .
  • the transponder microchip 35 may be powered through the inductive power coupling of the circuit of Figure 4 , and a battery need not be included .
  • the microchip and memory may also be operable with or without a broadcast electric field ( as in Figure 8 ) .
  • Figure 6 illustrates a SEEG system similar to the system shown in Figure 4 , in which the SEEG electrodes are powered with batteries instead of the inductive coupling shown in Figure 4 .
  • the system of Figure 6 includes the SEEG electrodes 3 , the conductors 9 , and NFC/RFID transponder 31 , but does not include the inductive power coupling 11 , patch electrode 10 , or subcutaneous electrodes 8 used to power the system of earlier figures . Instead, this system may be powered by batteries held in the transponder assembly 31 .
  • FIG. 7 illustrates an assembly of the NFC/RFID transponder 31 and a SEEG electrode 3 and NFC/RFID transponder microchip 35 , NFC/RFID antenna 36 and memory 37 .
  • This assembly includes a battery power supply 38 which powers the various components .
  • This system may use a separate NFC/RFID reader 32 for each NFC/RFID transponder 31 , or it may use a single NFC/RFID transponder 31 operable to interrogate and obtain EEG data from several NFC/RFID transponders 31 .
  • the NFC/RFID transponder is configured to store EEG data for transmission to a console or computer 41 which is configured to receive and store the EEG data, but is not configured to control the SEEG electrodes .
  • the system of Figures 6 and 7 may be used in a method in which a surgeon implants a number of SEEG electrodes 3 ( about 20 ) in the brain of a patient , in areas of the brain which may be the focus or origin of brain activity associated with a movement disorder , and places the NFC/RFID transponders 31 under the scalp of the patient , in the subcutaneous tissue 25 of the scalp (which may include connective tissue , epicranial apaneurosis , areolar connective tissue , and periosteum) ,
  • the surgeon or the patient may place an NFC/RFID reader 32 proximate an NFC/RFID transponder 31 to interrogate the transponders and obtain EEG data stored in the memory of the transponder .
  • the surgeon or the patient may use a dif ferent reader for each transponder , or may use a single reader to interrogate several , or all , of the transponders .
  • the readers may be maintained proximate the transponders , for substantially the entire period, and EEG data may be collected continuously while the coupling is maintained .
  • the transponders are self -powered and are operable to store historical EEG data
  • the surgeon or patient may bring the readers into proximity with the transponders only periodically, and the EEG data may be collected only periodically . This leaves the patient free to engage in normal activity, interrupted occasionally to interrogate the transponders , without the need for constant use of an appliance or head wear to keep the reader installed on the head in proximity to the transponders .
  • Figure 8 illustrates a SEEG system in which the SEEG electrodes are packaged along with the NFC/RFID components of Figure 5 or 7 in a single housing, and this combined electrode/transponder is secured to a tether not used for transmission of power or data and used only for retrieval of the combined electrode/transponder at the completion of the SEEG protocol .
  • the system of Figure 9 includes combined SEEG electrodes 3 and NFC/RFID transponders 31 in a combined assembly 51 .
  • the tether 52 may be electrically non-f unctional , and may serve only to facilitate removal of the combined assembly from the brain after completion of a SEEG protocol .
  • tabs 53 may be electrically non-f unctional , and may serve only to facilitate secure placement of the end of the tether under the scalp ( preventing migration through the insertion burr-hole , for example ) and to facilitate grasping of the ends of the tethers for removal of the combined assembly from the brain after completion of a SEEG protocol .
  • the tab may be omitted, and the end of the tether , unattached to any additional structure , may suf fice as a graspable feature suf ficient to retrieve the SEEG electrode assembly after the SEEG protocol is complete .
  • This system may use a power transmitting antenna 54 to power the electrodes and transponder components .
  • the antenna may also be configured as an NFC/RFID reader in place of readers 32 .
  • the control system 55 operable to transmit wireless power through the antenna to the electrode and transponder , may be used to control power applied through the hoop to the electrodes and transponder components .
  • the loop antenna and control system may be used in place of a reader to obtain sensor data from the electrodes .
  • this system may include memory and battery power disposed on the transponder , so that the reader may be used occasionally to collect EEG data collected over an extended period of time .
  • the transponder may be configured without an onboard power supply, and the antenna may be applied and operated continuously to provide power to the NFC/RFID transponder 31 , and the transformer may be configured without onboard memory, and the antenna used continuously to collect ECG data from the transponder .
  • Figure 9 illustrates the combined assembly 51 of the NFC/RFID transponder 31 and a SEEG electrode 3 and NFC/RFID transponder microchip 35 , NFC/RFID antenna 36 for use in the system shown in Figure 8.
  • this assembly may include a battery power supply 38 which powers the various components and memory 37 for storage of EEG data, in which case the data may be collected by occasional operation of the NFC/RFID reader 32 without the need to continuously wear and use the NFC/RFID reader 32.
  • the battery may be omitted and the combined assembly of the transponder may include a power converter 56 and the electrodes, transponder and memory may be powered by the power converter.
  • the power converter is powered wirelessly from the antenna external to the skull, disposed in an appliance or disguised as headwear, which is worn continuously while collecting EEG data (this may minimize the size of the implanted components but require continuous application of the appliance/headwear ) .
  • This system may use a separate NFC/RFID reader 32 for each NFC/RFID transponder 31, or it may use a single NFC/RFID transponder 31 operable to interrogate and obtain EEG data from several NFC/RFID transponders 31.
  • the system may include a plurality of SEEG electrode assemblies (3, 9, 8; 3, 9, 31, 3, 52, 53) , with each SEEG electrode assembly including a SEEG electrode (3) secured to a retrieval tether (9, 52) having a first end and a second end, the SEEG electrode (3) secured to the first end of the tether and a retrieval means (8, 31, 52) fixed to the second end of the tether, the retrieval means configured for temporary pericutaneous implantation in a scalp of the patient.
  • the system may further include a control system (12) configured to collect and store EEG data obtained from the SEEG electrodes and means for wirelessly communicating EEG data from the SEEG electrodes to the control system.
  • the method of obtaining EEG data from a patient's brain described above uses several of the SEEG electrode assemblies which each comprise a SEEG electrode 3 secured to a retrieval tether (9, 52) having a first end and a second end, with the SEEG electrode 8 secured to the first end of the tether.
  • the method includes the steps of providing a plurality of SEEG electrode assemblies (3, 9, 8; 9,31, 52,53) for temporary implantation into the brain, for the length of a SEEG protocol, which may be several days or weeks, and, preferably, removing the electrodes after sufficient data has been collected to diagnose a patient's condition, (2) providing a control system configured to collect and store EEG data obtained from the SEEG electrodes, (3) for each of the SEEG electrode assemblies, implanting the SEEG electrode in the patient's brain by inserting the SEEG electrode through a burr hole, with the tether running from the SEEG electrode and through the burr hole and securing the second end of the tether subcutaneously or supracutaneously outside the skull of the patient; (4) wirelessly communicating EEG data obtained from the SEEG electrodes to the control system, without connecting the SEEG electrodes to the control system with wires; and (5) after collecting EEG data from the SEEG electrodes, using the tether to remove the SEEG electrodes from the patient's brain.
  • the SEEG electrodes are implanted in the brain in a location known to effect target disorders, or known to produce signals indicative of target movement disorders, such as epilepsy.
  • doctors can collect EEG data and determine if the movement disorders are likely treatable with procedures such as resection of portions of the brain, stimulation of certain areas of the brain, or administration of drugs to the patient.
  • the SEEG electrode assembly may include an NFC/RFID transponder 31 fixed to the second end of the tether , and the method may include implanting the NFC/RFID transponder 31 pericutaneously , under or on the patient ' s scalp and wirelessly collecting EEG data from the SEEG electrodes using an NFC/RFID reader .
  • the method preferably includes removing the NFC/RFID transponder 31 from the patient ' s scalp, along the removing the SEEG electrodes from the brain (although the electrodes may be left in the brain for later EEG acquisition and administration of stimulation to the brain ) .
  • each SEEG electrode assembly may also comprise an electrically non-f unctional tab 53 fixed to the second end of the tether .
  • This version of the method further comprises the steps of implanting the electrically non-f unctional tab 53 pericutaneously, under or on the patient ' s scalp and wirelessly collecting EEG data from the SEEG electrodes using an NFC/RFID reader , and, after collecting EEG data from the SEEG electrodes , pulling the electrically nonfunctional tab 53 to remove the SEEG electrode from the patient ' s brain .
  • each SEEG electrode assembly may also comprises an electrode 8 fixed to the second end of the tether , wherein the tether comprises an electrical conductor , and the system includes at least one NFC/RFID transponder operable to transmit EEG data from the probes to an NFC/RFID reader .
  • This version of the method entails implanting the electrode 8 pericutaneously, under or on the patient ' s scalp, wirelessly collecting EEG data from the SEEG electrodes using an NFC/RFID reader , and, after collecting EEG data from the SEEG electrodes , pulling the electrode 8 to remove the SEEG electrode from the patient ' s brain .
  • Each of the versions of the system and methods can include means for wirelessly powering the SEEG electrodes , or a battery operably connected to the SEEG electrode , and any of the several powering systems and methods may be used with any of the EEG data sensing systems and methods .
  • Figure 10 illustrates a system for treatment of movement disorders using senor probes and stimulation probes operated by an external control system .
  • a patient 57 with a condition requiring deep brain stimulation ( DBS ) or diagnosis of a condition of the brain 58 is illustrated .
  • Figure 10 shows the placement of a plurality of probes 59 .
  • the probes may be stimulation probes , without sensing capability, or sensor probes without stimulation capability, or combined sensor and stimulation probes .
  • the sensor probes and stimulation probes can be inserted entirely within the brain at various positions .
  • Figure 1 also illustrates the scalp 60 , the skull 61 which is beneath the scalp, the dura 62 which is beneath the skull and the cerebral cortex 63 which is beneath the dura .
  • the probes 59 of Figure 10 are attached to electrodes 64 , which are implanted preferably in a subcutaneous location ( under the skin, superficial to the skull ) under the scalp, through conductors 65 .
  • the probes have been inserted into the brain of the patient through openings ( typically, burr-holes ) in the skull , and driven through the brain and deposited at a location determined by a surgeon and known to ef fect target disorders , or known to produce signals indicative of target disorders .
  • the electrodes 64 have been implanted subcutaneously, but may be installed supracutaneously or within the burr-holes .
  • the patch electrode 66 is disposed on the scalp, supracutaneously on the scalp, or subcutaneously under the scalp.
  • the patch electrode is, preferably, located such that it is not in direct physical contact with the electrodes 64, and is spaced from the electrodes 64.
  • the patch electrode 66 is connected to the secondary (remote) coupling component 67S 11S of a coupling assembly 67, and the primary (base) coupling component IIP is connected to the power supply and control system 68.
  • the coupling assembly is an inductive coupling assembly, comprising a pair of coils.
  • the secondary (remote) coupling component 11S may, like the patch electrode, also be installed on the scalp, supracutaneously, or subcutaneously under the scalp.
  • the primary (base) coupling component 67P may be placed in proximity to the secondary coupling using a magnetic attachment or other releasable attachment means (secured to a headband, glued to the overlying skin) or non- releasable means (stitched to the scalp, nailed or screwed to the skull, or other means not considered "releasable attachment means and require tools for removal) .
  • An insulated conductor 69 extends from the secondary (remote) coupling component 67S, through a burr-hole and into the brain (including the dura and the cortex) , and may be an insulated wire and include an electrode 70 at its distal end (a conductive wire, insulated or bare, will suffice) .
  • An additional conductor 71 connects the secondary (remote) coupling component 67S to the patch electrode 10.
  • the control system is configured to provide power to the probes, for stimulation of brain tissue proximate the probes, and receive sensor data from the probe.
  • the control system may operate as a DBS pulse generator, with or without further functionality .
  • the control system 68 may be further programmed to analyze the sensor data and modify control signals to the probes to control the stimulation provided by the probes in response to the sensor data .
  • the control system or console used to control the system and/or receive and store EEG data from the electrodes and provide bi-directional communications through the coupling, and provide stimulation pulses to the probed may be implemented on a dedicated console such as the Kohden Neurofax EEG-1200 console (without all the wires ) , and EEG monitoring system, a DBS pulse generator such as a Vercise GenusTM implantable pulse generator , a general-purpose computer , or a mobile phone or tablet .
  • the probe electrodes and electronics may be operable to detect native biological brain signals ( electrical activity of the brain ) , and generate electronic signals corresponding to native biological brain signals and transmit those electronic signals to the control system through the electrode 64 and patch electrode 66 and power coupling 67 .
  • the control system 68 is operable to receive electronic signals corresponding to native biological brain signals from the probes and, optionally, to interpret those signals .
  • the control system may also store this data, or transmit it elsewhere for storage and review.
  • control system may be configured, with appropriate programming, to analyze the electronic signals corresponding to native biological brain signals and determine whether the native biological brain signals are within a predetermined band of native biological brain signals , or above or below a predetermined threshold for the native biological brain signals , or characteristic of movement disorders .
  • the control system is may also be operable to generate and transmit control signals to the probes , to cause the probes to transmit stimulation pulses to structures within the brain to ef fect therapeutic changes in native biological brain signals .
  • the native biological brain signals of interest correspond to motor deficiencies , which may include Parkinson ' s Disease , epilepsy, essential tremors and/or dystonia .
  • the native biological brain signals may also be signals such as abnormal hyperactivity in Broadmann ' s area that correspond to mood disorders such as depression .
  • Stimulation can also be applied to areas of the dorsolateral prefrontal and lateral orbitof rental cortex for associative diseases involved in cognition or memory, to the limbic and paralimbic cortex, hippocampus and amygdala for the treatment of limbic ailments such as OCD or for treatment of pain management , stroke rehabilitation and cognition impairment .
  • Monitoring and stimulation can be in dif ferent locations of the brain , using some of the probes 59 in a sensing mode and using some of the probes 59 in a stimulation mode , and/or using some of the probes in both modes .
  • Figure 11 illustrates the probe 59 and subcutaneous electrode 64 .
  • the probe 59 includes several sensor/stimulation electrodes 77 , and may also include an LED assembly 78 which includes an LED 79 , and a power/signal contact 80 for providing power to the electrodes 77 and the LED 79 or transmitting electronic signals to the control system/console .
  • the sensor/stimulation electrodes are connected to the subcutaneous electrode 64 , and may be operated, in conjunction with the subcutaneous electrode 64 to apply electrical stimulation to brain tissue or sense electrical signals of the brain , or both .
  • the LED may be used to provide photonic stimulation of the brain .
  • Figure 11 also shows the conductor 65 and subcutaneous electrode 64 .
  • the subcutaneous electrode 64 which is preferably configured for implantation under the scalp, may consist of a bare conductive plate (metal such as stainless steel , or carbon , carbon fiber , glassy/pyrolytic carbon or graphene ) , but may also consist of a conductive plate covered in thin layer of insulation .
  • the subcutaneous electrode 64 may also comprise a near field communication coil (an NFC tag ) configured to communicate with the control system through a corresponding emitter and NFC controller of the control system (which may be housed proximate the patch electrode or housed in a separate appliance ) .
  • the conductor 65 also functions as a tether for retrieval of the probe from the brain .
  • the power /signal contact 80 on the probe tip may be bare , uncoated metal or other conductive material , or may be coated with a noninsulating coating with biologic ef fect , or covered in an insulating layer and work in conjunction with an insulated subcutaneous electrode 64 for capacitive coupling of both components of the probe to the conductor 69 of the secondary coil 67S .
  • FIG. 11 illustrates , in addition to the probe 59 , the components of the circuit and the circuit path for power and sensor signals .
  • power is supplied by the power supply, and is transmitted through conductor 81 to the primary ( base ) coupling component 67P , over the gap to the secondary ( remote ) coupling component 67S , and through the conductor 69 passing through the burr-hole and extending toward the brain 58 ( proximate the dura 62 , and preferably extending into the 7 cortex) .
  • the conductor 69 terminates proximate the dura, so the power and sensor signals pass through the cortex to the tip electrode 80 on the tip of the probe 59 , to power electronics on the probe associated with the LED or the stimulation electrodes .
  • the circuit is completed through the conductor 65 to the subcutaneous electrode 64 , through subcutaneous tissue 82 of the scalp (which may include connective tissue, epicranial apaneurosis, areolar connective tissue, and periosteum) , to the patch electrode 66, and through conductor 71 to the secondary (remote) coupling component 67S, across the air gap to the primary (base) coupling component 67P and thence to the power supply and control system.
  • the intracranial electrode 70 and the probe there is no wired connection between the intracranial electrode 70 and the probe, and there is no wired connection between the subcutaneous electrode and the patch electrode.
  • the skull serves as an insulator, separating the electrical conductor 69 terminus inside the skull (within the brain) from the subcutaneous electrode subcutaneous electrode 64 and patch electrode 66 which are both located superficial to the skull.
  • a system for sensing electrical activity of a brain of a patient may also include a probe (59) configured for implantation in the brain of the patient, and including means for sensing electrical activity of brain tissue (77, 78) .
  • the system may further include an inductive coupling assembly (67) including a primary (base) coupling component (67P) , secondary (remote) coupling component (67S) , said secondary (remote) coupling component (67S) configured for subcutaneous placement between the scalp and skull of the patient, said primary (base) coupling component (67P) configured for coupling with the secondary (remote) coupling component (67S) while disposed supracutaneously and proximate the secondary (remote) coupling component (67S) .
  • an inductive coupling assembly including a primary (base) coupling component (67P) , secondary (remote) coupling component (67S) , said secondary (remote) coupling component (67S) configured for subcutaneous placement between the scalp and skull of the patient, said primary (base) coupling component (67P) configured for coupling with the secondary (remote) coupling component (67S) while disposed supracutaneously and proximate the secondary (remote) coupling component (67S)
  • a patch electrode (66) may be configured for subcutaneous placement between the scalp and skull of the patient with a second electrical conductor (69) , said second electrical conductor (69) configured for electrically connecting the secondary (remote) coupling component (67S) to the brain of the patient.
  • the system may include a third electrical conductor (71) connecting the secondary (remote) coupling component (67S) to the patch electrode (66) and a control system operable connected to the primary (base) coupling component (67P) and operable to control the probe (59) to obtain signals corresponding to electrical activity of the brain and transmit electronic signals corresponding to the signals corresponding to electrical activity of the brain to the control system through the inductive coupling.
  • the control system may be operated to cause the probes to apply stimulation to structures in the brain proximate the probes .
  • the stimulation may be a voltage applied through one or more of the electrodes77. This voltage may be applied in bipolar mode (with a voltage differential between the electrodes) or monopolar mode (with a voltage differential applied between the patch electrode and the electrodes 77) .
  • the stimulation may be light emitted by the LED 79.
  • the control system may also be operated to cause the probes to sense electrical signal of the brain, particularly electrical signals associated with motor or mood disorders, and transmit those signals to the control system.
  • the control system may be operated to generate and display images corresponding to the sensed electrical signal, forward those signals to other computers for storage and analysis, or analyze those signals and determine, based on those signals, whether to apply stimulation through the probe to affect the brain.
  • electrical activity a brain of a patient is sensed by implanting a probe (59) configured for implantation in the brain of the patient, said probe (59) comprising a means for sensing electrical activity of brain tissue, and a power/signal contact for receiving power where the probe (59) is connected to a subcutaneous electrode (64) through a first electrical conductor (65) .
  • a subcutaneous electrode configured for implantation in the brain of the patient, said probe (59) comprising a means for sensing electrical activity of brain tissue, and a power/signal contact for receiving power where the probe (59) is connected to a subcutaneous electrode (64) through a first electrical conductor (65) .
  • a secondary (remote) is affixed to coupling component 67S of an inductive coupling assembly including a secondary (remote) coupling component (67S) and primary (base) coupling component (67P) to the scalp of the patient, pericutanously , and placing the primary (base) coupling component (67P) proximate the secondary (remote) coupling component (67S) .
  • a patch electrode (66) is implanted subcutaneously between the scalp and skull of the patient and the secondary (remote) is electrically connected to the coupling component (67S) to the brain of the patient through a second electrical connector (69) .
  • a secondary (remote) coupling component (67S) is electrically connected the to the patch electrode (66) through a third electrical conductor (71) and a power supply (68) is connected to the primary (base) coupling component (67P) and the power supply (68) is operated to cause the probe (59) to detect electrical activity of brain proximate the probe (59) and generate electronic signals corresponding to electrical activity and transmit those signals to a control system, through a circuit established from the secondary (remote) coupling component (67S) , through the second electrical connector (69) , through brain tissue to the power/signal contact, through the first electrical conductor
  • the probes are implanted within the brain and positioned in multiple regions of the brain subject to stimulation to af fect symptoms of a disease such as Parkinson ' s disease , epilepsy, essential tremor and dystonia .
  • the sensor components of the probes are operated to generate electronic signals corresponding to the sensed biological signals of the patient ' s brain .
  • the electronic signals are transmitted to the control system through the circuit illustrated in the Figures .
  • the control system may be programmed and configured to interpret whether the measured signal is within a predetermined band of signal readings , or above or below a predetermined threshold for the signal readings .
  • the control system may then also be operable to generate and transmit control signals to the probes , to cause the probes to transmit stimulation pulses to structures within the brain if the signal readings are determined to be outside of a predetermined range to ef fect therapeutic changes in native biological brain signals .
  • the control system may thus be programmed and operable to cause the probes to deliver a prescribed dosage of stimulation impulses to treat a variety of conditions and diseases such as Parkinson ' s disease , epilepsy, essential tremor and dystonia .
  • Sensor probes 59 inserted on or within the brain 58 detect and/or record signals linked to symptoms exhibited within the brain .
  • the sensor probes detect EEG , ECoG , AP , LFP or other detectable bio-signals .
  • the sensor probes transmit the electronic signal corresponding to the sensed bio-signal to the receiver of the control system .
  • the control system processes the electronic signal and is operable to transmit control signals to the stimulation probes to cause the stimulation probes to apply stimulation in response to variations in the sensed signals.
  • the sensor probes are operable to sense signals from the thalamus, STN, cortex or other associated structures of the brain, which are indicative of the conditions treated (signals indicative of reduced or increased unwanted motor activity in the patient, for example) .
  • Adjustment in the stimulation provided by the stimulation probes can also be made through operator input to the control system, in response to sensed signals from the sensor probes, for example in response to data provided by the control system through an output such as a display screen or audio speakers . Adjustment in the stimulation provided by the stimulation probes may also be made by the control system, without immediate operator input, if the control system is programmed to determine stimulation levels or patterns appropriate to apply or adjust in response to sensed signals from the sense probes. This realtime optimization would allow neurons the chance to rest and thus reduce overall deterioration over time.
  • the system may also include a method for applying stimulation to a brain of a patient including the steps of implanting a probe (59) configured for implantation in the brain of the patient, said probe (59) comprising a means for stimulating brain tissue, a power/signal contact for receiving power where the probe (59) is connected to a subcutaneous electrode (64) through a first electrical conductor (65) .
  • the method may further include the steps of implanting a patch electrode (66) subcutaneously between the scalp and skull of the patient, electrically connecting the secondary (remote) coupling component (67S) to the brain of the patient through a second electrical connector (69) and electrically connecting the secondary (remote) coupling component (67S) to the patch electrode (66) through a third electrical conductor (71) .
  • pericutaneous to refer to supracutaneous and subcutaneous place (that is, "near" the skin)
  • subcutaneous refers to its normally understood meaning of placement under the skin, but superficial to the skull
  • supracutaneous refers to its normally understood meaning of placement on the exterior surface of the skin (superficial to the skin) but not excluding the possibility of an intervening impedance matching substance, adhesive, cream or ointment or hair.

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Abstract

Les dispositifs et procédés décrits ci-dessous permettent de mettre en œuvre une stéréoélectroencéphalographie plus commode, ce qui peut permettre au patient de se déplacer librement pendant la période de surveillance de longue durée. Le système comprend un certain nombre d'électrodes SEEG de profondeur. Dans une version du système, chaque électrode SEEG est connectée sans fil à une console EEG, par l'intermédiaire d'une électrode sous-cutanée qui est connectée à l'électrode SEEG par l'intermédiaire d'un conducteur. L'électrode sous-cutanée est à son tour connectée sans fil à un appareil supracutané pouvant servir à obtenir des signaux SEEG, générés par l'électrode SEEG, par l'intermédiaire de l'électrode sous-cutanée. Le procédé d'utilisation implique l'implantation profonde des électrodes SEEG de profondeur dans le cerveau, l'implantation des électrodes sous-cutanées sous le cuir chevelu. Le patient n'a pas besoin d'être physiquement connecté à une console ou à un système de commande, et peut être hospitalisé en ambulatoire pendant la période de protocole SEEG.
PCT/US2023/066751 2022-05-10 2023-05-09 Système et procédé de surveillance et de stimulation cérébrale ambulatoire Ceased WO2023220573A2 (fr)

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US17/741,205 2022-05-10
US17/741,243 US20230363691A1 (en) 2022-05-10 2022-05-10 Ambulatory Brain Monitoring System and Method
US17/741,205 US20230364422A1 (en) 2022-05-10 2022-05-10 Deep Brain Stimulation System with Wireless Power
US17/741,243 2022-05-10

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CN119405322A (zh) * 2024-11-12 2025-02-11 南湖脑机交叉研究院 一种用于脑深部刺激的超声-脑电多功能电极

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WO2020185972A1 (fr) * 2019-03-11 2020-09-17 Rapoport Benjamin I Dispositifs, systèmes et procédés d'électroencéphalographie endovasculaire (eeg) et d'électrocorticographie (ecog)
US20210007602A1 (en) * 2019-07-12 2021-01-14 Neuralink Corp. Brain implant with subcutaneous wireless relay and external wearable communication and power device
WO2021055682A1 (fr) * 2019-09-18 2021-03-25 Duke University Réseaux d'électrodes d'électro-encéphalographie (eeg) et procédés d'utilisation associés

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN119405322A (zh) * 2024-11-12 2025-02-11 南湖脑机交叉研究院 一种用于脑深部刺激的超声-脑电多功能电极

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