WO2010042750A2 - System and method for miniature wireless implantable probe - Google Patents
System and method for miniature wireless implantable probe Download PDFInfo
- Publication number
- WO2010042750A2 WO2010042750A2 PCT/US2009/060048 US2009060048W WO2010042750A2 WO 2010042750 A2 WO2010042750 A2 WO 2010042750A2 US 2009060048 W US2009060048 W US 2009060048W WO 2010042750 A2 WO2010042750 A2 WO 2010042750A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- module
- neural
- probe
- intracorporeal
- signal
- Prior art date
Links
- 239000000523 sample Substances 0.000 title claims abstract description 143
- 238000000034 method Methods 0.000 title claims description 29
- 230000001537 neural effect Effects 0.000 claims abstract description 73
- 230000001766 physiological effect Effects 0.000 claims abstract description 12
- 238000004891 communication Methods 0.000 claims description 36
- 230000008878 coupling Effects 0.000 claims description 27
- 238000010168 coupling process Methods 0.000 claims description 27
- 238000005859 coupling reaction Methods 0.000 claims description 27
- 230000000638 stimulation Effects 0.000 claims description 16
- 230000000694 effects Effects 0.000 claims description 14
- 210000002569 neuron Anatomy 0.000 claims description 7
- 230000003834 intracellular effect Effects 0.000 claims description 6
- 238000007917 intracranial administration Methods 0.000 claims description 6
- 230000007177 brain activity Effects 0.000 claims description 4
- 210000004556 brain Anatomy 0.000 description 20
- 230000005540 biological transmission Effects 0.000 description 14
- 210000001519 tissue Anatomy 0.000 description 13
- 238000010586 diagram Methods 0.000 description 12
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 12
- HTXDPTMKBJXEOW-UHFFFAOYSA-N dioxoiridium Chemical compound O=[Ir]=O HTXDPTMKBJXEOW-UHFFFAOYSA-N 0.000 description 11
- 229910000457 iridium oxide Inorganic materials 0.000 description 11
- 239000004593 Epoxy Substances 0.000 description 8
- 210000003625 skull Anatomy 0.000 description 8
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 7
- 230000000747 cardiac effect Effects 0.000 description 7
- 238000002513 implantation Methods 0.000 description 7
- 230000001939 inductive effect Effects 0.000 description 7
- 229920001296 polysiloxane Polymers 0.000 description 7
- 229910052710 silicon Inorganic materials 0.000 description 7
- 239000010703 silicon Substances 0.000 description 7
- 241001465754 Metazoa Species 0.000 description 6
- 210000000278 spinal cord Anatomy 0.000 description 6
- 239000000758 substrate Substances 0.000 description 6
- 210000005013 brain tissue Anatomy 0.000 description 5
- 238000009413 insulation Methods 0.000 description 5
- 238000012544 monitoring process Methods 0.000 description 5
- 210000000578 peripheral nerve Anatomy 0.000 description 5
- 230000008569 process Effects 0.000 description 5
- 239000008393 encapsulating agent Substances 0.000 description 4
- 238000003199 nucleic acid amplification method Methods 0.000 description 4
- 206010042772 syncope Diseases 0.000 description 4
- 230000003321 amplification Effects 0.000 description 3
- 239000003990 capacitor Substances 0.000 description 3
- 238000005538 encapsulation Methods 0.000 description 3
- 206010015037 epilepsy Diseases 0.000 description 3
- 238000001914 filtration Methods 0.000 description 3
- 208000014674 injury Diseases 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 3
- 230000015654 memory Effects 0.000 description 3
- 210000003205 muscle Anatomy 0.000 description 3
- 230000007658 neurological function Effects 0.000 description 3
- 238000012805 post-processing Methods 0.000 description 3
- 206010010904 Convulsion Diseases 0.000 description 2
- 241000699670 Mus sp. Species 0.000 description 2
- 208000012902 Nervous system disease Diseases 0.000 description 2
- 210000004027 cell Anatomy 0.000 description 2
- 238000005520 cutting process Methods 0.000 description 2
- 230000006378 damage Effects 0.000 description 2
- 238000013480 data collection Methods 0.000 description 2
- 229910003460 diamond Inorganic materials 0.000 description 2
- 239000010432 diamond Substances 0.000 description 2
- 238000005530 etching Methods 0.000 description 2
- 238000007667 floating Methods 0.000 description 2
- 239000011521 glass Substances 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 239000012528 membrane Substances 0.000 description 2
- 230000003287 optical effect Effects 0.000 description 2
- 210000000056 organ Anatomy 0.000 description 2
- 238000004806 packaging method and process Methods 0.000 description 2
- 229910052697 platinum Inorganic materials 0.000 description 2
- 238000012545 processing Methods 0.000 description 2
- 238000011084 recovery Methods 0.000 description 2
- 238000011160 research Methods 0.000 description 2
- 230000008054 signal transmission Effects 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- 230000008733 trauma Effects 0.000 description 2
- 208000020446 Cardiac disease Diseases 0.000 description 1
- 206010007559 Cardiac failure congestive Diseases 0.000 description 1
- 208000000094 Chronic Pain Diseases 0.000 description 1
- 229920001651 Cyanoacrylate Polymers 0.000 description 1
- 206010019233 Headaches Diseases 0.000 description 1
- 206010019280 Heart failures Diseases 0.000 description 1
- MWCLLHOVUTZFKS-UHFFFAOYSA-N Methyl cyanoacrylate Chemical compound COC(=O)C(=C)C#N MWCLLHOVUTZFKS-UHFFFAOYSA-N 0.000 description 1
- 208000002193 Pain Diseases 0.000 description 1
- 208000018737 Parkinson disease Diseases 0.000 description 1
- 239000004809 Teflon Substances 0.000 description 1
- 229920006362 Teflon® Polymers 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- YJZATOSJMRIRIW-UHFFFAOYSA-N [Ir]=O Chemical class [Ir]=O YJZATOSJMRIRIW-UHFFFAOYSA-N 0.000 description 1
- 238000009825 accumulation Methods 0.000 description 1
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- PNEYBMLMFCGWSK-UHFFFAOYSA-N aluminium oxide Inorganic materials [O-2].[O-2].[O-2].[Al+3].[Al+3] PNEYBMLMFCGWSK-UHFFFAOYSA-N 0.000 description 1
- 238000000231 atomic layer deposition Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 239000000560 biocompatible material Substances 0.000 description 1
- 210000004903 cardiac system Anatomy 0.000 description 1
- 230000001413 cellular effect Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000004590 computer program Methods 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000007850 degeneration Effects 0.000 description 1
- 238000000151 deposition Methods 0.000 description 1
- 230000008021 deposition Effects 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 208000035475 disorder Diseases 0.000 description 1
- 230000002526 effect on cardiovascular system Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 239000003292 glue Substances 0.000 description 1
- 231100000869 headache Toxicity 0.000 description 1
- 230000036541 health Effects 0.000 description 1
- 208000019622 heart disease Diseases 0.000 description 1
- 210000005003 heart tissue Anatomy 0.000 description 1
- 210000001320 hippocampus Anatomy 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 230000006698 induction Effects 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 210000004072 lung Anatomy 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 201000006417 multiple sclerosis Diseases 0.000 description 1
- 210000000653 nervous system Anatomy 0.000 description 1
- 210000003061 neural cell Anatomy 0.000 description 1
- 230000000926 neurological effect Effects 0.000 description 1
- 230000003955 neuronal function Effects 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 239000004065 semiconductor Substances 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 239000010409 thin film Substances 0.000 description 1
- 238000000427 thin-film deposition Methods 0.000 description 1
- 238000012546 transfer Methods 0.000 description 1
- 238000012795 verification Methods 0.000 description 1
- 230000003245 working effect Effects 0.000 description 1
- 210000000707 wrist Anatomy 0.000 description 1
Classifications
-
- 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
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
-
- 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]
-
- 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
- A61B5/40—Detecting, measuring or recording for evaluating the nervous system
- A61B5/4029—Detecting, measuring or recording for evaluating the nervous system for evaluating the peripheral nervous systems
- A61B5/4041—Evaluating nerves condition
-
- 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
-
- 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
-
- 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
- A61N1/37252—Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
- A61N1/37288—Communication to several implantable medical devices within one patient
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0004—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the type of physiological signal transmitted
- A61B5/0006—ECG or EEG signals
-
- 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
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/283—Invasive
-
- 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
- A61N1/36082—Cognitive or psychiatric applications, e.g. dementia or Alzheimer's 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
- A61N1/37205—Microstimulators, e.g. implantable through a cannula
-
- 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
- A61N1/37223—Circuits for electromagnetic coupling
- A61N1/37229—Shape or location of the implanted or external antenna
-
- 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
- A61N1/375—Constructional arrangements, e.g. casings
- A61N1/3756—Casings with electrodes thereon, e.g. leadless stimulators
Definitions
- Damage to a cardiac or nervous system can result in diverse disorders, ranging from headaches to Alzheimer, Parkinson, epilepsy, multiple sclerosis, etc.
- the result can include degeneration in the patient's quality of life.
- it can be beneficial to observe, record, stimulate, or otherwise understand the inner workings of the cardiac, neural, or other physiological system.
- the present subject matter includes a system comprising a miniature wireless device suitable for implantation and configured to provide a variety of services including any combination of physiological monitoring, data recording, and stimulation.
- the system includes one or more probes configured for implantation.
- a probe according to the present subject matter can be fabricated with physical dimensions suitable for measurement in the range of tens or hundreds of micrometers, and is sometimes referred to as a nanoprobe or nanofabricated probe.
- a microprobe in contrast, has physical dimensions measured in the range of millimeters.
- the probe of the present subject matter can include a communication portion and a data collection portion, a stimulation portion, or both a data collection portion and a stimulation portion.
- a particular probe can operate independent of other probes or a single probe can operate in concert with one or more other probes.
- the communication portion of the probe is configured to communicate with an implantable module.
- the module sometimes referred to herein as an intracorporeal module, is configured for implantation within an organ or a body.
- the module communicates with one or more probes using an intra-body (or intracorporeal) communication link, sometimes referred to as IBCOM (for intra- body communication or intra-brain communication).
- IBCOM intra-body communication or intra-brain communication
- the communication entails a low power transmission via near- field electrostatic coupling, and can include, but is not limited to, inductive coupling or capacitive coupling.
- two or more probes can also communicate with each other using intracorporeal communication.
- One or more probes can be implanted in a particular body.
- the device sizes and communication protocols are configured for reduced trauma to tissue and thus allow use of a probe at sensitive sites such as fragile tissue or moving tissue areas.
- sensitive sites include a spinal cord, cardiac tissue, and lung tissue.
- An example of the present system or method can be used for, among other things, functional electric stimulation of a spinal cord, peripheral nerves, muscles (e.g., for treatment of chronic pain, urology, stroke recovery, etc.), or one or more other organs or physiologic systems, such as the cardiovascular or the neural system, deep brain stimulation (DBS) (e.g., for treatment of Parkinson's disease, epilepsy, depression, etc.), cardiac or neural monitoring (e.g., for syncope, unexplained seizures, fainting, etc.), neural prosthetics or brain-machine interfaces, neuroscience research, or one or more other uses.
- DBS deep brain stimulation
- cardiac or neural monitoring e.g., for syncope, unexplained seizures, fainting, etc.
- Example 1 includes a system having a neural probe and an intracorporeal module.
- the neural probe is configured to detect physiological activity and to wirelessly transmit a first signal based on the physiological activity.
- the intracorporeal module is communicatively coupled to the neural probe.
- the intracorporeal module is configured to receive the first signal from the neural probe.
- Example 2 includes the system of example 1 and wherein the intracorporeal module is configured to transmit a second signal based on receipt of the first signal.
- the system includes an external device that is communicatively coupled to the intracorporeal module.
- the external device is configured to receive the second signal from the intracorporeal module and to record data corresponding to the physiological activity.
- Example 3 includes the system of example 1 wherein the physiological activity includes at least one of an intracellular signal and an extracellular signal from at least one neuron.
- Example 4 includes the system of example 3, wherein the physiological activity includes an intracellular signal from a single neuron.
- Example 5 includes the system of example 1, wherein the neural probe includes a plurality of neural probes and the intracorporeal module is configured to receive a plurality of first signals.
- Example 6 includes the system of example 5, wherein at least two probes of the plurality of neural probes have independent electrical grounds.
- Example 7 includes system of example 1, wherein the neural probe includes a first plurality and a second plurality of neural probes.
- the intracorporeal module includes a first and second intracorporeal module.
- the first plurality of neural probes is communicatively coupled to the first intracorporeal module and the second plurality of neural probes is communicatively coupled to the second intracorporeal module.
- the first intracorporeal module and the second intracorporeal module are communicatively coupled to the external device.
- Example 8 includes the system of example 1, wherein the neural probe is configured to couple to the intracorporeal module using near field electrostatic coupling.
- Example 9 includes the system of example 8, wherein the near field electrostatic coupling is isolated from normal neural activity.
- Example 10 includes the system of example 1, wherein at least one of a neural probe and the intracorporeal module is configured to deliver electrical stimulation to a tissue proximate to the at least one of the neural probe and the intracorporeal module.
- Example 11 includes a system having an implantable neural probe.
- the implantable neural probe is configured to detect brain activity and to wirelessly transmit a signal based on the detected brain activity to an intra-cranial module using near field electrostatic coupling.
- the implantable neural probe and the intra-cranial module are located proximate a neuron.
- the near field electrostatic coupling is independent of normal neural activity.
- Example 12 includes a system having an implantable probe.
- the implantable probe is configured to detect electrical activity and to wirelessly transmit a signal based on the detected electrical activity to an intra-body module using near field electrostatic coupling.
- the near field electrostatic coupling is independent of normal electrical activity of the body.
- Example 13 includes a method.
- the method includes detecting electrophysiological activity using an implanted probe.
- the method includes generating an electrical signal using the electrophysiological activity.
- the method includes wirelessly communicating the electrical signal to an intracorporeal module and exchanging communications between the intracorporeal module and an external device.
- FIG. 1 illustrates a brain and a plurality of neural probes.
- FIGS. 2A and 2B illustrate views of a neural probe.
- FIG. 3 illustrates a block diagram of a system.
- FIG. 4 illustrates a block diagram of a system.
- FIG. 5 illustrates a block diagram of a system.
- FIG. 6 illustrates a feedback arrangement.
- FIG. 7 illustrates a block diagram of a system.
- FIG. 8 illustrates a block diagram of a system.
- FIG. 9 illustrates a block diagram of a system.
- FIGS. 10, 11, and 12 illustrate partially fabricated probes.
- FIGS. 13 and 14 illustrate views of a probe.
- FIG. 15 illustrates a block diagram of a method.
- FIG. 1 illustrates system 1OA.
- System 1OA includes portions of an implantable probe system for monitoring a physiological parameter.
- system 1OA is configured to monitor a physiological parameter of body 15A having brain 20.
- Probes 25 A, 25B, and 25C are representative of a plurality of probes distributed throughout various portions of brain 20.
- Each probe is in communication with intracorporeal module 35A.
- Intracorporeal module 35A is disposed within body 15 A.
- system 1OA illustrates antenna 40 coupled to intracorporeal module 35A. Antenna 40 enables extracorporeal communications between intracorporeal module 35A and an external device (not shown in this figure).
- Probes 25A, 25B, and 25C are coupled to intracorporeal module 35A by wireless links 3OA, 3OB, and 3OC, respectively.
- links 3OA, 3OB, and 3OC are configured for communicating through tissue.
- a signal can be communicated within the body using low power devices while providing low loss and high data rates.
- An example of the present subject matter enables intra-brain communication in which the brain acts as a conductive media to transmit the signals to an intracorporeal module, as shown in FIG. 1.
- the voltage and current of the communicated signal is configured for biocompatibility.
- the voltage, current, and frequency level are configured to achieve a desired data transmission rate and quality of service without injury to the brain tissue.
- the brain (or other tissue) can function as a conductive transmitting media, and compared with other wireless communication schemes, offers low power, low noise, and smaller size (no antenna or coils used).
- a data modulation scheme is implemented in order to send processed and measured neural signals from each probe free of conflict from other probes.
- the modulation scheme is free of charge accumulation in brain tissue and uses a unique identifier for each probe, allows low complexity for small size implementation, and operates using low power budget.
- Suitable data modulation schemes include a binary frequency shift keying (BFSK) modulator at the output of each probe.
- a demodulator is located at the intracorporeal module or located at an external receiving unit.
- FIGS. 2A and 2B illustrate views of probe 25D.
- the view of FIG. 2A depicts coil 45 on a surface of probe 25D. Coil 45 provides electrical power for a circuit of probe 25D.
- FIG. 2A also illustrates reference electrode 55 and ground electrode 50.
- Module 65 includes an analog front end and digitization circuitry.
- Module 60 includes modulation circuitry.
- Modules 65 and 60 are electrically coupled to active electrodes 70 and IBCOM electrode 58.
- probe 25D has a length L of 500 ⁇ m, depth D of lOO ⁇ m, and height H of lOO ⁇ m, however, other dimensions are also contemplated, including, for example, approximately 2mm x lmm x 0.5mm. Smaller dimensions are also contemplated.
- one example of the present subject matter includes three electrical access sites on the probe: an active electrode, a reference electrode and an amplifier electrode. A differential signal is measured between the active electrode and the reference electrode. The active electrode, sized larger than the other electrodes, is connected to amplifier isolated ground of the probe.
- One example of the present subject matter includes the active electrode and the reference electrode and operates without direct connection to the floating ground of the amplifier.
- FIG. 3 illustrates a block diagram of probe 25E, intracorporeal module 35A, and cell 95A (for example, a brain neural cell).
- probe 25E includes module 65 coupled to reference electrode 55, ground electrode 50, and active electrode 70.
- Module 65 includes an analog front end having preamplifier 90, postprocessing unit 85, and analog-to-digital (A/D) converter 68.
- Postprocessing unit 85 can include, for example a filter (such as a band-pass filter). After A/D conversion by converter 68, the digital output is further modulated (by modulator 60) and converted to current and then transmitted wirelessly through brain tissue (via intra-brain communication or IBCOM electrode 30D) to intracorporeal module 35A.
- Intracorporeal module 35A is configured to receive the data from probe 25E and configured to process and send the data to the external device (not shown in this figure).
- RF inductive link 80 can include a coil.
- IBCOM is communication using the brain (or body) as the transmitting media.
- Biological tissue is generally transparent at very high frequencies. Communication can be conducted in biological tissue at frequencies ranging from 100 kHz to 50 MHz.
- Active electrode 70 disposed on the surface of probe 25E is configured to measure a neural signal or other physiological signal.
- Reference electrode 55 provides differential recordings.
- a third (multipart) electrode, such as electrode 50, provides a local ground connection.
- the electrodes are connected to the electronic circuitry of probe 25E.
- the electronic circuitry of probe 25E includes various components, some of which may include for example, an analog front end, a digital converter, a modulation section and a voltage/current converter.
- electrode 3OD of probe 25E includes iridium oxide (IrOx).
- the modulated current can be communicated using electrode 3OD.
- electrode 3OD is relatively large due to its high charge injection capacity and tissue biocompatibility.
- the probe can be fabricated using nanofabrication techniques.
- An example of the present subject matter includes a fabricated chip and a microcircuit having a miniaturized amplifier configured to amplify neural signals by 44 dB (15Ox), while reducing DC-offset by more than 8OdB.
- This configuration provides extremely large post-amplification signal to DC Noise ratios.
- the amplifier circuit occupies a smaller area on chip and consumes lower power.
- FIG. 4 illustrates probes 25F, 25G, and 25H disposed in body 15B.
- Probes 25F, 25G, and 25H are configured to detect a physiological parameter associated with each of neuron 95B, 95C, and 95D, respectively.
- probes 25F, 25G, and 25H can be widely distributed throughout body 15B.
- Each of probes 25F, 25G, and 25H includes a wireless communication module that uses an electrode to communicatively couple with the tissue.
- FIG. 4 illustrates intracorporeal modules 35B and 35C disposed within body 15B. Intracorporeal modules 35B and 35C each includes a wireless communication module, here again denoted by an electrode.
- Intracorporeal module 35B is configured to communicate with any or all of probes 25F, 25G, and 25H, as indicated by the dashed lines.
- intracorporeal module 35C is configured to communicate with any or all of probes 25F, 25G, and 25H, as indicated by the dashed lines.
- the electrodes in this example, are configured for electrostatic coupling, and in one example, this includes capacitive coupling wherein a change in potential on a first electrode can be detected by a second electrode that is separated from the first electrode by a distance.
- Intracorporeal modules 35B and 35C are in communication with external device 100.
- Intracorporeal modules 35B and 35C can be coupled by a wired or wireless link with external device 100.
- the link is transdermal.
- Intracorporeal modules 35B and 35C are configured for implantation within tissue of body 15B. Intracorporeal modules 35B and 35C can be disposed within a skull and probes 25F, 25G, and 25H can be disposed within a brain, as depicted in FIG. 1. Intracorporeal modules 35B and 35C and probes 25F, 25G, and 25H each has an electrical ground that is independent of a ground of any other device. That is, intracorporeal module 35B has an electrical ground that is independent of a ground potential used by probe 25F.
- the communication between the various intracorporal elements of the present subject matter is configured to avoid or mitigate interference with normal neurological functions.
- the amplitude and frequency of an exchanged signal is sufficiently low to allow communications to proceed independent of normal neurological functions. That is, the communication (via electrostatic coupling in one example) is isolated from normal neural activity.
- FIG. 5 illustrates probe 25 J coupled to power unit 135.
- the coupling denoted in the figure by the pair of vertical dashed lines, can include near field electrostatic coupling, such as inductive coupling or capacitive coupling.
- probe 25 J includes module 105, here denoted as an analog front end and IBCOM.
- Module 105 is coupled to power module 125 by lines 110, 115, and 120.
- Power module 125 includes a rectifier and a power recovery circuit.
- Line 110 carries a supply voltage depicted as Vcc
- line 115 provides a ground or reference voltage
- line 120 carries voltage V EE - Power module 125 is electrically coupled to coil 130.
- Coil 130, of probe 25J, in the example shown, is inductively coupled to coil 137 of power unit 135.
- Coil 137 is also coupled to controller 138 of power unit 135.
- the efficiency of the power delivery to an implantable probe 25J depends on factors such as the distance between the external transmitter (coil 137) and the telemetry IC (coupled to coil 130 of probe 25J), alignment of the internal coil (coil 130) to the external coil (coil 137), RF frequency, and external unit to power.
- the present subject matter includes inductive coupling powering.
- Power can be delivered to a low power implantable prosthesis processor (IPP) via inductive coupling.
- IPP implantable prosthesis processor
- coupling can be maximized by aligning the source magnetic field with the sensing coil that is implemented on the IPP chip. Field alignment can be accomplished using multiple source coils which are dynamically excited to optimize the magnetic field direction for maximum power transfer.
- inductive coupling can be used to send data from the intracorporeal module to the probe (such as a nanoprobe) to perform operations such as neural stimulation and power shutdown (to enter a standby mode).
- a probe includes a microbattery attached to the backside part instead of the coil.
- FIG. 6 illustrates a block diagram of system 200.
- System 200 includes elements of a front end for a probe, such as probe 25 J.
- System 200 provides a bioamplifier (including pre-amplification and post-processing) and filtration as shown in the figure.
- System 200 amplifies, filters, and converts the neural signal received at neural interface 205 into a digital output provided at output 235 by means of a sigma-delta modulator.
- the sigma-delta modulator allows miniaturization.
- FIG. 6 illustrates a second-order modulator and allows control of the coefficients Al, A2 and feedback to tailor amplification and filtration parameters.
- the sigma- delta modulator has sensitivity in the microvolt region.
- the amplifier in integrator 215 and integrator 225 is fully differential, thus providing improved power supply rejection, common mode rejection, and dynamic range.
- the input pairs of the integrators amplifiers can include both NMOS and PMOS transistors to increase dynamic range and further reduce noise.
- the integrator uses switched capacitor circuits.
- System 200 includes summation node 210 configured to receive a signal from neural interface 205 and feedback 245. An output of summation node 210 is coupled to integrator 215. Summation node 220 is configured to receive an output from integrator 215 and feedback 240. An output of summation node 220 is coupled to integrator 225. An output of integrator 225 is coupled to feedback 240, feedback 245, and to quantizer 230. An output of quantizer 230 is coupled to output 235 as shown in the figure.
- FIG. 7 illustrates block diagram of system 300 suitable for IBCOM.
- System 300 includes ROM 305 coupled to MUX 310.
- ROM 305 includes a read-only-memory and MUX 310 includes a multiplexor.
- MUX 310 is coupled to VCO 315, a voltage controlled oscillator.
- An output of VCO 315 is coupled to converter 320.
- Converter 320 includes a voltage-to-current converter.
- An output of converter 320 is coupled to electrode 325, here depicted as an IrOx electrode.
- System 300 includes packaging 340 having the aforementioned circuit as well as power regulator 330 and battery 335, as shown.
- FIG. 8 illustrates block diagram of system 400 suitable for miniaturized recording.
- System 400 includes electrodes A and R coupled to amplifier 415 by link 405 and link 410, respectively. Electrodes A and R, in one example, denote active and reference, respectively.
- Links 405 and 410 provide AC coupling and include a filter as depicted in the figure.
- An output of amplifier 415 is coupled to low pass filter 420 and an output of filter 420 is coupled to analog-to-digital converter 425.
- Converter 425 provides a double ended output.
- System 400 includes packaging 430 having the aforementioned circuit as well as power regulator 330 and battery 335, as shown.
- FIG. 9 illustrates a block diagram of system 500.
- System 500 depicts an arrangement for IBCOM communication with body 15C, here denoted as a brain.
- synthesized data is generated by units 520 and 530 and an analog signal is communicated to body 15C by IBCOM 540.
- body 15C provides an analog signal that is communicated by IBCOM 540 to unit 510.
- unit 510 is configured to generate a representation of data provided by units 520 and 530.
- IBCOM 540 includes IrOx recording electrode, a multichannel IrOx transmitting electrode and a single IrOx transmitting electrode.
- An integrated chip for a wireless multi-channel neural recording system is configured to separate the microvolt-level neural signals from the much larger millivolt-level DC offsets.
- the integrated chip is to provide very high data rate transmission of the digitized neural signals.
- FIGS. 10, 11, and 12 illustrate partially fabricated probes.
- FIG. 10 illustrates dicing.
- FIG. 11 illustrates probe 1100 having substrate 1110 and angular face 1105 set at angle ⁇ .
- FIG. 12 illustrates chip 1115 coupled to substrate 1110 by bonding 1120 and encapsulation 1125.
- a CMOS chip can be sub-diced using a diamond wafer saw.
- the chip can be placed on top of UV tape (120 microns thick) to help hold it together after cutting.
- a diamond blade (with 50 micron maximal kerf) can be used (at 4mm/sec) to sub-dice the chip.
- the actual kerf can be measured and used in conjunction with the optical alignment and micrometer tools on the saw to position the saw for cutting the CMOS chip.
- DI and N2 can be used to clean the surface, and each cut can be visually inspected to insure the quality of the cut and to confirm that the circuitry is not damaged by the cut.
- the UV tape can be released with a 5 minute exposure to a flood exposure system.
- the chips can be handled using ESD-safe tweezers and grounded wrist bands.
- a 500 micron thick, 100mm diameter silicon wafer (or substrate) can be diced into small spears with a sharp tip. Multiple parallel cuts can be made 500 microns apart using the same process as above.
- angle ⁇ is 15 degrees, however, other values can also be used.
- the angular rotation produces spears having a rectangular cross-section of 500 ⁇ m x 500 ⁇ m, and a length of 4-5cm long, and with a 15 degree tip angle.
- the sharp, chisel-like tip shape is configured to reduce trauma to brain tissue during insertion.
- the length can be selected so that the device reaches the hippocampus (a deep brain structure).
- the silicon spears can then be insulated with a 1000 Angstrom layer of alumina on all four sides using atomic layer deposition.
- Three 50 micron platinum (Pt) wires insulated with Teflon for an outer diameter of 100 microns, stripped of two cm of insulation at one end, can be tensioned to lay in parallel along the top of a silicon spear.
- the insulation stripped ends can be positioned so that the bare wires ran along the spear for three mm behind the taper where the insulation began.
- UV tape in one mm strips
- Epoxy can be applied in a thin film across the tops of the wires exclusive of the taped regions and a five mm length behind the stripped wires (epoxy on two mm exposed un-insulated un-taped wire).
- wires can be cut 1.5 mm behind silicon taper and then flush at the other end of the silicon spear to free the spear/wire combination from wire tensioning device. Spears can then be fixed to a solid surface using double sided tape and a high speed drill turning a burr in order to expose one mm of the glued un-insulated Pt wire and create a flat surface. A spot of epoxy can then be applied to the silicon spear on the 1.5mm flat length in front of the exposed Pt wire and behind the taper. The CMOS chip can then be set on the glue and adjusted to align the wires with the pads (Vdd, IBCOM, and ground). After curing, wire bonding can be applied using 0.001" aluminum wire. A wire bond that separates prior to encapsulation can be reconnected to the Pt wire using conductive epoxy.
- FIG. 12 depicts CMOS chip 1115 electrically coupled by wire bonding 1120.
- Encapsulant 1125 can include silicone to encapsulate the CMOS chip, wire bond wire, and exposed portions of the platinum wire. Silicone is a biocompatible material with good dielectric properties and provides good efficiency in encapsulating neurological implants. Silicone can be applied using a glob-top method.
- the packaged chip can then be connected to the PCB with a direct wire connection from IBCOM to the PCB. After testing and verification, the middle platinum wire (connecting the IBCOM pad) can be cut to expose a platinum cross- section. The exposed cross section is configured to be free of insulation and encapsulant.
- the packaged chip can then be attached to a glass slide using epoxy and the wires soldered to connecting pins. A micromanipulator can be used to hold the glass slide and deliver the probe to a test site or to a monitoring site.
- FIGS. 13 and 14 illustrate views of a probe. In FIG. 13, the angular face of substrate 1110 is disposed on one end and wires 1130 disposed on an opposing end.
- Chip 1115 is wire bonded, by bonding 1120, to wires 1130 and encapsulated by encapsulant 1125.
- chip 610 has dimensions of 570 ⁇ m by 930 ⁇ m. In the figure, chip 610 is affixed to a portion of probe 600.
- the electrode for data communication can be fabricated of Pt or IrOx. In one example, the electrode provides an area of exposed Pt of 2000 ⁇ m 2 (50 ⁇ m diameter circle).
- the chip can be affixed to the substrate using epoxy, cyanoacrylate, or silicone.
- the encapsulant can include silicone.
- Fabrication of the neural probe can include semiconductor fabrication processes such as deposition and etching. For example, thin-film deposition can be used to fabricate leads, provide insulation. Etching can be used to fabricate a CMOS cavity and to configure the probe shape. Other fabrication processes can include integration such as dicing the CMOS chip, epoxy bonding the CMOS chip to the probe, and wirebonding the CMOS chip pads to the probe.
- the present subject matter is encapsulated.
- Encapsulation can include applying a volume of epoxy or silicone to protect the device.
- FIG. 15 illustrates method 700 according to one example.
- Method 700 includes, at 705, detecting electrophysiological activity. The activity can be detected by a probe, such as an implanted probe.
- method 700 includes generating an electrical signal using the electrophysiological activity. In one example, this includes processing through a front end which can include amplification, filtration, and other processing.
- method 700 includes wirelessly communicating the electrical signal to an intracorporeal module.
- Wirelessly communicating can include using an intra-brain communication channel.
- the intracorporeal module can be disposed within a skull of a person or animal.
- method 700 includes exchanging communications between the intracorporeal module and an external device.
- the external device can include a data recorder, a display device, a computer, or other such device.
- the communications can be exchanged using a wired link or a wireless link.
- a neural probe includes a cellular- sized or subcellular- sized device configured to measure an electrical signal (voltage, current, resistance or other electrical parameter) and transmitting them wirelessly to an intracorporeal module.
- the intracorporeal module is configured for implantation in a large, accommodating structure (such as a ventricle).
- the intracorporeal module is connected, using, for example, a miniature (standard) wire connection to a headstage and transmission device (cabled) or a wireless connection, to a data recording device.
- the probe separates the data recording site from the transmission mechanism, thus simplifying multi- structure recordings in animals and also enables recording data from fragile structures (such as a spinal cord or peripheral nerves).
- the present subject matter also enhances the stability of recordings in animals having thin skulls (such as mice or songbirds).
- An example of the present subject matter is insensitive to movement of the patient.
- An example of the present subject matter decouples the data recording site from the skull and musculature, thus providing more stable signals.
- the probe is configured to simplify recording from multiple structures, thus allowing interaction studies and studies at the level of the functional system rather than at a single structure.
- the present subject matter allows recordings from fragile structures (such as the eye) in freely-behaving animals. Additionally, the probe simplifies the recording from non-brain structures, such as spinal cord and peripheral nerves.
- the probe may be able to record from violently moving structures such as cardiac or other muscle tissue.
- the probe is configured for stimulation. As such, the probe can be used for deep-brain stimulation. Stimulation may also include heart stimulation or motor muscle stimulation.
- an intracellular probe is provided to cross the neural membrane of a single cell and transmit the membrane potential to the intracorporeal module.
- a miniature recording device (such as a probe as described here, and having a scale of less than 300 ⁇ m x 50 ⁇ m x 50 ⁇ m) is configured to measure the voltage differential between two recording sites and transmit that measurement intra-cranially (through the intra-cranial medium) to an implanted device referred to as an intracorporeal module.
- an intracorporeal module is configured for implantation in the ventricle and has a scale of less than 1 mm diameter.
- the intracorporeal module is connected through a fine wire to a transmission device on the top of the skull.
- This transmission device can be configured for wired communication.
- the communication system is configured to communicate light via fiber-optical cables, light signals transmitted through the air, or wirelessly.
- An example of the present subject matter includes transmission configured to transmit neural data over 802.1 Ib protocols wirelessly.
- the system can accommodate 50 ⁇ V-1000 ⁇ V peak voltages, and transmits 4 channels at 20 kHz/channel with 12 bit resolution.
- the system communicates using standard Ethernet packets using the UDP protocol.
- the signal transmission loss between the transmitting and receiving electrodes (I recei v ed/Lent) has an average loss of less than 17dB (7x reduction) including losses due to electrode impedance.
- Lower impedance iridium oxide electrodes can be used for lower losses and reduced power.
- An example of the present subject matter is configured for simplified implantation and provides massively parallel, wireless neural probes, capable of recording data from tens to hundreds to thousands of sites simultaneously.
- the probe is configured for extracellular use or intracellular use.
- the present subject matter includes an implantable, low power, and distributed probe system configured to use intra-brain communication.
- the probes can be distributed throughout the brain and operate using very low power.
- the plurality of probes communicates with an external device by means of an implantable intracorporeal module.
- the plurality of probes communicate over a distance of a few centimeters with the intracorporeal module.
- the intracorporeal module communicates directly with the external device through either a wired link or a wireless link
- cardiac events can be monitored by a device configured to provide pressure data (such as associated with congestive heart failure) or ECG information (such as syncope, unexplained seizures or fainting).
- ECG information such as syncope, unexplained seizures or fainting.
- neural events can be monitored such as, for example,
- Epilepsy monitoring or a neuro stimulator allows for multiple devices in disparate parts of the brain.
- the present subject matter can be used for neural prosthetic devices and brain-machine interfaces.
- Other applications include recording data from brain, spinal cord, and peripheral nerves.
- the recording or stimulation device can include a neural nanofabricated probe.
- the neural probe can include a cellular, a subcellular, or other miniature device capable of measuring a voltage signal and wirelessly transmitting the voltage signal to an intracorporeal module implanted in an accommodating structure, or capable of delivering an electrical stimulation.
- the intracorporeal module can be connected to a headstage or other device using wire connection, and to a data recording device using a wire or wireless connection.
- the probe can separate the recording site from the transmission mechanism, which can simplify multi- structure recordings in awake, behaving animals, can enable the recording from fragile structures such as spinal cord or peripheral nerves, and can enhance the stability of recordings in animals with thin skulls such as mice or songbirds. These advances can also make the recording device insensitive to movement of the patient, simplifying the clinical use of these devices in human patients.
- Activated Iridium Oxide (a IrOx) electrodes can be implanted and sine waves transmitted from a source to a sink located some distance (such as 5 mm, 10 mm, or 15 mm) from the source. In one example, frequencies from 10 ⁇ 5 Hz to 10 ⁇ 8
- the brain can provide for reliable transmission of signals with little current loss up to the megahertz range.
- Frequencies of 100-500 kHz can be used for signals. These frequencies are high enough to not interfere with normal neuronal function, and low enough to provide reliable transmission across a greater than 1 cm range.
- multiple access schemes for intra-brain communication between a probe and an intracorporeal module, can be managed in a number of different ways.
- one scheme can include frequency division multiplexing.
- multiple probes can be configured to communicate simultaneously to the intracorporeal module (or to multiple intracorporeal modules) at separate frequencies.
- 100/200 kHz and 300/400 kHz can be used for transmit and receive for two separate probes.
- other schemes such as frequency, phase, or amplitude modulation based schemes can be used for the intra-brain communication.
- Global Common Ground The following section describes a configuration and method concerning an electrical ground for one example of recording signals without a common global ground reference potential.
- a body-based ground is provided by a skull screw.
- the probe can be configured with three electrode sites: a differential signal between active and reference electrodes, and a larger electrode connected to amplifier isolated ground.
- the probe can be configured with an active electrode and a reference electrode without direct connection the amplifier' s floating ground. The following section describes a configuration for transmission using separate grounds.
- a signal can be transmitted (e.g., in the brain) from a transmitter to a receiver using separate grounds.
- a signal can be transmitted through brain tissue using current transmission (in contrast to other technologies, such as RF and induction).
- two IrOx electrodes can be implanted into a brain.
- the first electrode serves as the source to provide a realistic simulated neural signal
- the second electrode serves as the sink to receive the transmission.
- the simulated neural signal provided at the source can be compared to the signal received at the sink.
- each component e.g., the transmitter and the receiver
- three IrOx electrodes can be implanted into a brain.
- the simulated neural signal and the received neural signal can be separately sent, received, and then demodulated to reconstruct the two signals.
- Two simulated neural signals can be taken from measured data, and each component can be powered by separate battery packs having separate grounds.
- Method examples described herein can be machine or computer- implemented at least in part. Some examples can include a computer-readable medium or machine-readable medium encoded with instructions operable to configure an electronic device to perform methods as described in the above examples.
- An implementation of such methods can include code, such as microcode, assembly language code, a higher-level language code, or the like. Such code can include computer readable instructions for performing various methods. The code may form portions of computer program products. Further, the code may be tangibly stored on one or more volatile or non-volatile computer-readable media during execution or at other times.
- These computer- readable media may include, but are not limited to, hard disks, removable magnetic disks, removable optical disks (e.g., compact disks and digital video disks), magnetic cassettes, memory cards or sticks, random access memories (RAMs), read only memories (ROMs), and the like.
- RAMs random access memories
- ROMs read only memories
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- General Health & Medical Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Veterinary Medicine (AREA)
- Biomedical Technology (AREA)
- Public Health (AREA)
- Heart & Thoracic Surgery (AREA)
- Neurology (AREA)
- Neurosurgery (AREA)
- Molecular Biology (AREA)
- Medical Informatics (AREA)
- Surgery (AREA)
- Psychology (AREA)
- Physics & Mathematics (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Radiology & Medical Imaging (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Cardiology (AREA)
- Computer Networks & Wireless Communication (AREA)
- Physiology (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
A system includes a neural probe and an intracorporeal module. The probe, such as a nanoprobe, is configured to detect physiological activity and to wirelessly transmit a first signal based on the physiological activity. The intracorporeal module is communicatively coupled to the neural probe, the intracorporeal module configured to receive the first signal from the neural probe.
Description
SYSTEM AND METHOD FOR MINIATURE WIRELESS IMPLANTABLE PROBE
CLAIM OF PRIORITY
This document claims the benefit of priority, under 35 U.S.C. Section
119(e), to Aaron David Redish et al., U.S. Provisional Patent Application Serial Number 61/104,214, entitled "SYSTEM AND METHOD FOR MINATURE WIRELESS IMPLANTABLE ELECTRICAL RECORDING OR STIMULATION," filed on October 9, 2009 (Attorney Docket No. 600.722PRV), and is incorporated herein by reference.
STATEMENT REGARDING UNITED STATES OF AMERICA FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT
This invention was made with government support under award number T90-DK70106 from the National Institutes of Health (NIH). The government has certain rights in this invention.
BACKGROUND
Damage to a cardiac or nervous system can result in diverse disorders, ranging from headaches to Alzheimer, Parkinson, epilepsy, multiple sclerosis, etc. For patients suffering from any type of cardiac or neurological disorder, the result can include degeneration in the patient's quality of life. In designing a treatment for the cardiac or the neurological disorder, it can be beneficial to observe, record, stimulate, or otherwise understand the inner workings of the cardiac, neural, or other physiological system.
OVERVIEW In one example, the present subject matter includes a system comprising a miniature wireless device suitable for implantation and configured to provide a variety of services including any combination of physiological monitoring, data recording, and stimulation. In one example, the system includes one or more probes configured for implantation. A probe, according to the present subject matter can be fabricated with physical dimensions suitable for measurement in
the range of tens or hundreds of micrometers, and is sometimes referred to as a nanoprobe or nanofabricated probe. A microprobe, in contrast, has physical dimensions measured in the range of millimeters.
The probe of the present subject matter can include a communication portion and a data collection portion, a stimulation portion, or both a data collection portion and a stimulation portion. A particular probe can operate independent of other probes or a single probe can operate in concert with one or more other probes.
The communication portion of the probe is configured to communicate with an implantable module. The module, sometimes referred to herein as an intracorporeal module, is configured for implantation within an organ or a body. The module communicates with one or more probes using an intra-body (or intracorporeal) communication link, sometimes referred to as IBCOM (for intra- body communication or intra-brain communication). The communication entails a low power transmission via near- field electrostatic coupling, and can include, but is not limited to, inductive coupling or capacitive coupling. In addition to intracorporeal communications between a probe and a module, two or more probes can also communicate with each other using intracorporeal communication. One or more probes can be implanted in a particular body. The device sizes and communication protocols are configured for reduced trauma to tissue and thus allow use of a probe at sensitive sites such as fragile tissue or moving tissue areas. Examples of sensitive sites include a spinal cord, cardiac tissue, and lung tissue. An example of the present system or method can be used for, among other things, functional electric stimulation of a spinal cord, peripheral nerves, muscles (e.g., for treatment of chronic pain, urology, stroke recovery, etc.), or one or more other organs or physiologic systems, such as the cardiovascular or the neural system, deep brain stimulation (DBS) (e.g., for treatment of Parkinson's disease, epilepsy, depression, etc.), cardiac or neural monitoring (e.g., for syncope, unexplained seizures, fainting, etc.), neural prosthetics or brain-machine interfaces, neuroscience research, or one or more other uses.
Example 1 includes a system having a neural probe and an intracorporeal module. The neural probe is configured to detect physiological activity and to wirelessly transmit a first signal based on the physiological activity. The intracorporeal module is communicatively coupled to the neural probe. The intracorporeal module is configured to receive the first signal from the neural probe.
Example 2 includes the system of example 1 and wherein the intracorporeal module is configured to transmit a second signal based on receipt of the first signal. The system includes an external device that is communicatively coupled to the intracorporeal module. The external device is configured to receive the second signal from the intracorporeal module and to record data corresponding to the physiological activity.
Example 3 includes the system of example 1 wherein the physiological activity includes at least one of an intracellular signal and an extracellular signal from at least one neuron.
Example 4 includes the system of example 3, wherein the physiological activity includes an intracellular signal from a single neuron.
Example 5 includes the system of example 1, wherein the neural probe includes a plurality of neural probes and the intracorporeal module is configured to receive a plurality of first signals.
Example 6 includes the system of example 5, wherein at least two probes of the plurality of neural probes have independent electrical grounds.
Example 7 includes system of example 1, wherein the neural probe includes a first plurality and a second plurality of neural probes. In addition, the intracorporeal module includes a first and second intracorporeal module. The first plurality of neural probes is communicatively coupled to the first intracorporeal module and the second plurality of neural probes is communicatively coupled to the second intracorporeal module. The first intracorporeal module and the second intracorporeal module are communicatively coupled to the external device.
Example 8 includes the system of example 1, wherein the neural probe is configured to couple to the intracorporeal module using near field electrostatic coupling.
Example 9 includes the system of example 8, wherein the near field electrostatic coupling is isolated from normal neural activity.
Example 10 includes the system of example 1, wherein at least one of a neural probe and the intracorporeal module is configured to deliver electrical stimulation to a tissue proximate to the at least one of the neural probe and the intracorporeal module.
Example 11 includes a system having an implantable neural probe. The implantable neural probe is configured to detect brain activity and to wirelessly transmit a signal based on the detected brain activity to an intra-cranial module using near field electrostatic coupling. The implantable neural probe and the intra-cranial module are located proximate a neuron. The near field electrostatic coupling is independent of normal neural activity.
Example 12 includes a system having an implantable probe. The implantable probe is configured to detect electrical activity and to wirelessly transmit a signal based on the detected electrical activity to an intra-body module using near field electrostatic coupling. The near field electrostatic coupling is independent of normal electrical activity of the body.
Example 13 includes a method. The method includes detecting electrophysiological activity using an implanted probe. In addition, the method includes generating an electrical signal using the electrophysiological activity. Furthermore, the method includes wirelessly communicating the electrical signal to an intracorporeal module and exchanging communications between the intracorporeal module and an external device.
This overview is intended to provide an overview of subject matter of the present patent application. It is not intended to provide an exclusive or exhaustive explanation of the invention. The detailed description is included to provide further information about the present patent application.
BRIEF DESCRIPTION OF THE DRAWINGS In the drawings, which are not necessarily drawn to scale, like numerals may describe similar components in different views. Like numerals having different letter suffixes may represent different instances of similar components.
The drawings illustrate generally, by way of example, but not by way of limitation, various embodiments discussed in the present document. FIG. 1 illustrates a brain and a plurality of neural probes. FIGS. 2A and 2B illustrate views of a neural probe. FIG. 3 illustrates a block diagram of a system.
FIG. 4 illustrates a block diagram of a system. FIG. 5 illustrates a block diagram of a system. FIG. 6 illustrates a feedback arrangement. FIG. 7 illustrates a block diagram of a system. FIG. 8 illustrates a block diagram of a system.
FIG. 9 illustrates a block diagram of a system. FIGS. 10, 11, and 12 illustrate partially fabricated probes. FIGS. 13 and 14 illustrate views of a probe. FIG. 15 illustrates a block diagram of a method.
DETAILED DESCRIPTION
FIG. 1 illustrates system 1OA. System 1OA includes portions of an implantable probe system for monitoring a physiological parameter. In the figure, system 1OA is configured to monitor a physiological parameter of body 15A having brain 20. Probes 25 A, 25B, and 25C are representative of a plurality of probes distributed throughout various portions of brain 20. Each probe is in communication with intracorporeal module 35A. Intracorporeal module 35A is disposed within body 15 A. In addition, system 1OA illustrates antenna 40 coupled to intracorporeal module 35A. Antenna 40 enables extracorporeal communications between intracorporeal module 35A and an external device (not shown in this figure).
Probes 25A, 25B, and 25C are coupled to intracorporeal module 35A by wireless links 3OA, 3OB, and 3OC, respectively. As noted elsewhere in this document, links 3OA, 3OB, and 3OC are configured for communicating through tissue.
A signal can be communicated within the body using low power devices while providing low loss and high data rates. An example of the present subject
matter enables intra-brain communication in which the brain acts as a conductive media to transmit the signals to an intracorporeal module, as shown in FIG. 1.
The voltage and current of the communicated signal is configured for biocompatibility. In addition, the voltage, current, and frequency level are configured to achieve a desired data transmission rate and quality of service without injury to the brain tissue.
The brain (or other tissue) can function as a conductive transmitting media, and compared with other wireless communication schemes, offers low power, low noise, and smaller size (no antenna or coils used). A data modulation scheme is implemented in order to send processed and measured neural signals from each probe free of conflict from other probes. The modulation scheme is free of charge accumulation in brain tissue and uses a unique identifier for each probe, allows low complexity for small size implementation, and operates using low power budget. Suitable data modulation schemes include a binary frequency shift keying (BFSK) modulator at the output of each probe. A demodulator is located at the intracorporeal module or located at an external receiving unit.
The communicated signal is encoded and communicated in a manner that does not interfere with normal neurological functions. FIGS. 2A and 2B illustrate views of probe 25D. The view of FIG. 2A depicts coil 45 on a surface of probe 25D. Coil 45 provides electrical power for a circuit of probe 25D. FIG. 2A also illustrates reference electrode 55 and ground electrode 50.
The view of FIG. 2B depicts module 65 and module 60. Module 65 includes an analog front end and digitization circuitry. Module 60 includes modulation circuitry. Modules 65 and 60 are electrically coupled to active electrodes 70 and IBCOM electrode 58.
In the example shown, probe 25D has a length L of 500μm, depth D of lOOμm, and height H of lOOμm, however, other dimensions are also contemplated, including, for example, approximately 2mm x lmm x 0.5mm. Smaller dimensions are also contemplated.
Rather than body-based common ground (such as provided by an electrical connection via a skull screw), one example of the present subject
matter includes three electrical access sites on the probe: an active electrode, a reference electrode and an amplifier electrode. A differential signal is measured between the active electrode and the reference electrode. The active electrode, sized larger than the other electrodes, is connected to amplifier isolated ground of the probe.
One example of the present subject matter includes the active electrode and the reference electrode and operates without direct connection to the floating ground of the amplifier.
FIG. 3 illustrates a block diagram of probe 25E, intracorporeal module 35A, and cell 95A (for example, a brain neural cell). In the example shown, probe 25E includes module 65 coupled to reference electrode 55, ground electrode 50, and active electrode 70. Module 65 includes an analog front end having preamplifier 90, postprocessing unit 85, and analog-to-digital (A/D) converter 68. Postprocessing unit 85 can include, for example a filter (such as a band-pass filter). After A/D conversion by converter 68, the digital output is further modulated (by modulator 60) and converted to current and then transmitted wirelessly through brain tissue (via intra-brain communication or IBCOM electrode 30D) to intracorporeal module 35A.
Intracorporeal module 35A is configured to receive the data from probe 25E and configured to process and send the data to the external device (not shown in this figure).
Power 75 for probe 25E is provided by RF inductive link 80. In one example, RF inductive link 80 can include a coil.
IBCOM is communication using the brain (or body) as the transmitting media. Biological tissue is generally transparent at very high frequencies. Communication can be conducted in biological tissue at frequencies ranging from 100 kHz to 50 MHz.
Active electrode 70, disposed on the surface of probe 25E is configured to measure a neural signal or other physiological signal. Reference electrode 55 provides differential recordings. A third (multipart) electrode, such as electrode 50, provides a local ground connection. The electrodes are connected to the electronic circuitry of probe 25E. The electronic circuitry of probe 25E includes
various components, some of which may include for example, an analog front end, a digital converter, a modulation section and a voltage/current converter.
In one example, electrode 3OD of probe 25E includes iridium oxide (IrOx). The modulated current can be communicated using electrode 3OD. In one example, electrode 3OD is relatively large due to its high charge injection capacity and tissue biocompatibility. The probe can be fabricated using nanofabrication techniques.
An example of the present subject matter includes a fabricated chip and a microcircuit having a miniaturized amplifier configured to amplify neural signals by 44 dB (15Ox), while reducing DC-offset by more than 8OdB. This configuration provides extremely large post-amplification signal to DC Noise ratios. The amplifier circuit occupies a smaller area on chip and consumes lower power.
FIG. 4 illustrates probes 25F, 25G, and 25H disposed in body 15B. Probes 25F, 25G, and 25H are configured to detect a physiological parameter associated with each of neuron 95B, 95C, and 95D, respectively. As noted in FIG. 1, probes 25F, 25G, and 25H can be widely distributed throughout body 15B. Each of probes 25F, 25G, and 25H includes a wireless communication module that uses an electrode to communicatively couple with the tissue. In addition, FIG. 4 illustrates intracorporeal modules 35B and 35C disposed within body 15B. Intracorporeal modules 35B and 35C each includes a wireless communication module, here again denoted by an electrode. Intracorporeal module 35B is configured to communicate with any or all of probes 25F, 25G, and 25H, as indicated by the dashed lines. In addition, intracorporeal module 35C is configured to communicate with any or all of probes 25F, 25G, and 25H, as indicated by the dashed lines. The electrodes, in this example, are configured for electrostatic coupling, and in one example, this includes capacitive coupling wherein a change in potential on a first electrode can be detected by a second electrode that is separated from the first electrode by a distance.
Each of intracorporeal modules 35B and 35C are in communication with external device 100. Intracorporeal modules 35B and 35C can be coupled by a
wired or wireless link with external device 100. In one example, the link is transdermal.
Intracorporeal modules 35B and 35C are configured for implantation within tissue of body 15B. Intracorporeal modules 35B and 35C can be disposed within a skull and probes 25F, 25G, and 25H can be disposed within a brain, as depicted in FIG. 1. Intracorporeal modules 35B and 35C and probes 25F, 25G, and 25H each has an electrical ground that is independent of a ground of any other device. That is, intracorporeal module 35B has an electrical ground that is independent of a ground potential used by probe 25F. In addition, the communication between the various intracorporal elements of the present subject matter is configured to avoid or mitigate interference with normal neurological functions. In particular, the amplitude and frequency of an exchanged signal is sufficiently low to allow communications to proceed independent of normal neurological functions. That is, the communication (via electrostatic coupling in one example) is isolated from normal neural activity.
FIG. 5 illustrates probe 25 J coupled to power unit 135. The coupling, denoted in the figure by the pair of vertical dashed lines, can include near field electrostatic coupling, such as inductive coupling or capacitive coupling. In the figure, probe 25 J includes module 105, here denoted as an analog front end and IBCOM. Module 105 is coupled to power module 125 by lines 110, 115, and 120. Power module 125 includes a rectifier and a power recovery circuit. Line 110 carries a supply voltage depicted as Vcc, line 115 provides a ground or reference voltage, and line 120 carries voltage VEE- Power module 125 is electrically coupled to coil 130.
Coil 130, of probe 25J, in the example shown, is inductively coupled to coil 137 of power unit 135. Coil 137 is also coupled to controller 138 of power unit 135.
The efficiency of the power delivery to an implantable probe 25J depends on factors such as the distance between the external transmitter (coil 137) and the telemetry IC (coupled to coil 130 of probe 25J), alignment of the internal coil (coil 130) to the external coil (coil 137), RF frequency, and external unit to power.
In one example, the present subject matter includes inductive coupling powering. Power can be delivered to a low power implantable prosthesis processor (IPP) via inductive coupling. According to one example, coupling can be maximized by aligning the source magnetic field with the sensing coil that is implemented on the IPP chip. Field alignment can be accomplished using multiple source coils which are dynamically excited to optimize the magnetic field direction for maximum power transfer. Additionally, inductive coupling can be used to send data from the intracorporeal module to the probe (such as a nanoprobe) to perform operations such as neural stimulation and power shutdown (to enter a standby mode).
In one example, to address variability in the physical distance and alignment parameters during surgical procedures, multiple coils can be utilized in the upper portion of the head to enhance diversity of the transmitted signal power and to reduce the effect of misalignment. In one example, a probe includes a microbattery attached to the backside part instead of the coil.
FIG. 6 illustrates a block diagram of system 200. System 200 includes elements of a front end for a probe, such as probe 25 J. System 200 provides a bioamplifier (including pre-amplification and post-processing) and filtration as shown in the figure.
System 200 amplifies, filters, and converts the neural signal received at neural interface 205 into a digital output provided at output 235 by means of a sigma-delta modulator. The sigma-delta modulator allows miniaturization. FIG. 6 illustrates a second-order modulator and allows control of the coefficients Al, A2 and feedback to tailor amplification and filtration parameters. The sigma- delta modulator has sensitivity in the microvolt region. The amplifier in integrator 215 and integrator 225 is fully differential, thus providing improved power supply rejection, common mode rejection, and dynamic range. The input pairs of the integrators amplifiers can include both NMOS and PMOS transistors to increase dynamic range and further reduce noise. The integrator uses switched capacitor circuits. The common-mode control block in the amplifier uses switched capacitor technique to provide good linearity, low power consumption, and low noise.
System 200 includes summation node 210 configured to receive a signal from neural interface 205 and feedback 245. An output of summation node 210 is coupled to integrator 215. Summation node 220 is configured to receive an output from integrator 215 and feedback 240. An output of summation node 220 is coupled to integrator 225. An output of integrator 225 is coupled to feedback 240, feedback 245, and to quantizer 230. An output of quantizer 230 is coupled to output 235 as shown in the figure.
FIG. 7 illustrates block diagram of system 300 suitable for IBCOM. System 300 includes ROM 305 coupled to MUX 310. ROM 305 includes a read-only-memory and MUX 310 includes a multiplexor. MUX 310 is coupled to VCO 315, a voltage controlled oscillator. An output of VCO 315 is coupled to converter 320. Converter 320 includes a voltage-to-current converter. An output of converter 320 is coupled to electrode 325, here depicted as an IrOx electrode. System 300 includes packaging 340 having the aforementioned circuit as well as power regulator 330 and battery 335, as shown.
FIG. 8 illustrates block diagram of system 400 suitable for miniaturized recording. System 400 includes electrodes A and R coupled to amplifier 415 by link 405 and link 410, respectively. Electrodes A and R, in one example, denote active and reference, respectively. Links 405 and 410 provide AC coupling and include a filter as depicted in the figure. An output of amplifier 415 is coupled to low pass filter 420 and an output of filter 420 is coupled to analog-to-digital converter 425. Converter 425 provides a double ended output.
System 400 includes packaging 430 having the aforementioned circuit as well as power regulator 330 and battery 335, as shown.
FIG. 9 illustrates a block diagram of system 500. System 500 depicts an arrangement for IBCOM communication with body 15C, here denoted as a brain. In the figure, synthesized data is generated by units 520 and 530 and an analog signal is communicated to body 15C by IBCOM 540. In addition, body 15C provides an analog signal that is communicated by IBCOM 540 to unit 510. As shown, unit 510 is configured to generate a representation of data provided by units 520 and 530.
IBCOM 540 includes IrOx recording electrode, a multichannel IrOx transmitting electrode and a single IrOx transmitting electrode.
An integrated chip for a wireless multi-channel neural recording system is configured to separate the microvolt-level neural signals from the much larger millivolt-level DC offsets. In addition, the integrated chip is to provide very high data rate transmission of the digitized neural signals.
The present subject matter includes a miniaturized amplifier capable of performing DC-cancellation without the use of capacitors, which decreased the total size and power draw. FIGS. 10, 11, and 12 illustrate partially fabricated probes. FIG. 10 illustrates dicing. FIG. 11 illustrates probe 1100 having substrate 1110 and angular face 1105 set at angle α. FIG. 12 illustrates chip 1115 coupled to substrate 1110 by bonding 1120 and encapsulation 1125.
A CMOS chip can be sub-diced using a diamond wafer saw. The chip can be placed on top of UV tape (120 microns thick) to help hold it together after cutting. A diamond blade (with 50 micron maximal kerf) can be used (at 4mm/sec) to sub-dice the chip.
After calibration cuts, the actual kerf can be measured and used in conjunction with the optical alignment and micrometer tools on the saw to position the saw for cutting the CMOS chip. After each cut, DI and N2 can be used to clean the surface, and each cut can be visually inspected to insure the quality of the cut and to confirm that the circuitry is not damaged by the cut. After all cuts, the UV tape can be released with a 5 minute exposure to a flood exposure system. The chips can be handled using ESD-safe tweezers and grounded wrist bands. A 500 micron thick, 100mm diameter silicon wafer (or substrate) can be diced into small spears with a sharp tip. Multiple parallel cuts can be made 500 microns apart using the same process as above. Then one cut can be made after an angular rotation of the platform, thus providing angle α as shown in FIGS. 11 and 12. In one example, angle α is 15 degrees, however, other values can also be used. In the example shown, the angular rotation produces spears having a rectangular cross-section of 500μm x 500μm, and a length of 4-5cm long, and with a 15 degree tip angle. The sharp, chisel-like tip shape is configured to reduce trauma to brain tissue during insertion. The length can be selected so that the device reaches the hippocampus (a deep brain structure). The silicon spears can then be
insulated with a 1000 Angstrom layer of alumina on all four sides using atomic layer deposition.
Three 50 micron platinum (Pt) wires, insulated with Teflon for an outer diameter of 100 microns, stripped of two cm of insulation at one end, can be tensioned to lay in parallel along the top of a silicon spear. The insulation stripped ends can be positioned so that the bare wires ran along the spear for three mm behind the taper where the insulation began. UV tape (in one mm strips) can be laid atop the wires across the spear at roughly one cm intervals beginning just behind the taper. Epoxy can be applied in a thin film across the tops of the wires exclusive of the taped regions and a five mm length behind the stripped wires (epoxy on two mm exposed un-insulated un-taped wire). After curing, wires can be cut 1.5 mm behind silicon taper and then flush at the other end of the silicon spear to free the spear/wire combination from wire tensioning device. Spears can then be fixed to a solid surface using double sided tape and a high speed drill turning a burr in order to expose one mm of the glued un-insulated Pt wire and create a flat surface. A spot of epoxy can then be applied to the silicon spear on the 1.5mm flat length in front of the exposed Pt wire and behind the taper. The CMOS chip can then be set on the glue and adjusted to align the wires with the pads (Vdd, IBCOM, and ground). After curing, wire bonding can be applied using 0.001" aluminum wire. A wire bond that separates prior to encapsulation can be reconnected to the Pt wire using conductive epoxy. FIG. 12 depicts CMOS chip 1115 electrically coupled by wire bonding 1120.
Encapsulant 1125 can include silicone to encapsulate the CMOS chip, wire bond wire, and exposed portions of the platinum wire. Silicone is a biocompatible material with good dielectric properties and provides good efficiency in encapsulating neurological implants. Silicone can be applied using a glob-top method.
The packaged chip can then be connected to the PCB with a direct wire connection from IBCOM to the PCB. After testing and verification, the middle platinum wire (connecting the IBCOM pad) can be cut to expose a platinum cross- section. The exposed cross section is configured to be free of insulation and encapsulant. The packaged chip can then be attached to a glass slide using epoxy and the wires soldered to connecting pins. A micromanipulator can be used to hold the glass slide and deliver the probe to a test site or to a monitoring site.
FIGS. 13 and 14 illustrate views of a probe. In FIG. 13, the angular face of substrate 1110 is disposed on one end and wires 1130 disposed on an opposing end. Chip 1115 is wire bonded, by bonding 1120, to wires 1130 and encapsulated by encapsulant 1125. In FIG. 14, chip 610 has dimensions of 570μm by 930μm. In the figure, chip 610 is affixed to a portion of probe 600.
Other configurations are also contemplated, including, for example a substrate of silicon, high modulus silicone, or other sufficiently rigid material. The electrode for data communication can be fabricated of Pt or IrOx. In one example, the electrode provides an area of exposed Pt of 2000μm2 (50μm diameter circle). The chip can be affixed to the substrate using epoxy, cyanoacrylate, or silicone. The encapsulant can include silicone.
Fabrication of the neural probe can include semiconductor fabrication processes such as deposition and etching. For example, thin-film deposition can be used to fabricate leads, provide insulation. Etching can be used to fabricate a CMOS cavity and to configure the probe shape. Other fabrication processes can include integration such as dicing the CMOS chip, epoxy bonding the CMOS chip to the probe, and wirebonding the CMOS chip pads to the probe.
In one example, the present subject matter is encapsulated. Encapsulation can include applying a volume of epoxy or silicone to protect the device.
FIG. 15 illustrates method 700 according to one example. Method 700 includes, at 705, detecting electrophysiological activity. The activity can be detected by a probe, such as an implanted probe. At 710, method 700 includes generating an electrical signal using the electrophysiological activity. In one example, this includes processing through a front end which can include amplification, filtration, and other processing.
At 715, method 700 includes wirelessly communicating the electrical signal to an intracorporeal module. Wirelessly communicating can include using an intra-brain communication channel. The intracorporeal module can be disposed within a skull of a person or animal.
At 720, method 700 includes exchanging communications between the intracorporeal module and an external device. The external device can include a
data recorder, a display device, a computer, or other such device. The communications can be exchanged using a wired link or a wireless link.
Additional Aspects This document describes neural probe devices, systems, as well as methods of fabricating and using a probe. A neural probe includes a cellular- sized or subcellular- sized device configured to measure an electrical signal (voltage, current, resistance or other electrical parameter) and transmitting them wirelessly to an intracorporeal module. The intracorporeal module is configured for implantation in a large, accommodating structure (such as a ventricle). The intracorporeal module is connected, using, for example, a miniature (standard) wire connection to a headstage and transmission device (cabled) or a wireless connection, to a data recording device. The probe separates the data recording site from the transmission mechanism, thus simplifying multi- structure recordings in animals and also enables recording data from fragile structures (such as a spinal cord or peripheral nerves). The present subject matter also enhances the stability of recordings in animals having thin skulls (such as mice or songbirds).
An example of the present subject matter is insensitive to movement of the patient.
An example of the present subject matter decouples the data recording site from the skull and musculature, thus providing more stable signals. The probe is configured to simplify recording from multiple structures, thus allowing interaction studies and studies at the level of the functional system rather than at a single structure. The present subject matter allows recordings from fragile structures (such as the eye) in freely-behaving animals. Additionally, the probe simplifies the recording from non-brain structures, such as spinal cord and peripheral nerves. The probe may be able to record from violently moving structures such as cardiac or other muscle tissue. In one example, the probe is configured for stimulation. As such, the probe can be used for deep-brain stimulation. Stimulation may also include heart stimulation or motor muscle stimulation.
In one example, an intracellular probe is provided to cross the neural membrane of a single cell and transmit the membrane potential to the intracorporeal module.
In one example, a miniature recording device (such as a probe as described here, and having a scale of less than 300 μm x 50 μm x 50 μm) is configured to measure the voltage differential between two recording sites and transmit that measurement intra-cranially (through the intra-cranial medium) to an implanted device referred to as an intracorporeal module. One example of an intracorporeal module is configured for implantation in the ventricle and has a scale of less than 1 mm diameter. The intracorporeal module is connected through a fine wire to a transmission device on the top of the skull. This transmission device can be configured for wired communication. In one example, the communication system is configured to communicate light via fiber-optical cables, light signals transmitted through the air, or wirelessly.
Wireless Transmission
An example of the present subject matter includes transmission configured to transmit neural data over 802.1 Ib protocols wirelessly. The system can accommodate 50μV-1000μV peak voltages, and transmits 4 channels at 20 kHz/channel with 12 bit resolution. The system communicates using standard Ethernet packets using the UDP protocol.
Transmitting signals through the intra-cranial tissue
In one example, multiple sinusoidal signals are transmitted through the brain (at frequencies of 100 kHz to 50MHz, mean electrode impedance = 65kΩ, current amplitude =100μA). The signal transmission loss between the transmitting and receiving electrodes (I received/Lent) has an average loss of less than 17dB (7x reduction) including losses due to electrode impedance. Lower impedance iridium oxide electrodes can be used for lower losses and reduced power.
An example of the present subject matter is configured for simplified implantation and provides massively parallel, wireless neural probes, capable of recording data from tens to hundreds to thousands of sites simultaneously. In
various examples, the probe is configured for extracellular use or intracellular use.
In one example, the present subject matter includes an implantable, low power, and distributed probe system configured to use intra-brain communication. The probes can be distributed throughout the brain and operate using very low power. The plurality of probes communicates with an external device by means of an implantable intracorporeal module. The plurality of probes communicate over a distance of a few centimeters with the intracorporeal module. The intracorporeal module communicates directly with the external device through either a wired link or a wireless link
An example of the present subject matter can be used for recording. For example, cardiac events can be monitored by a device configured to provide pressure data (such as associated with congestive heart failure) or ECG information (such as syncope, unexplained seizures or fainting). In addition, neural events can be monitored such as, for example,
Epilepsy monitoring or a neuro stimulator. The present subject matter allows for multiple devices in disparate parts of the brain. In addition, the present subject matter can be used for neural prosthetic devices and brain-machine interfaces. Other applications include recording data from brain, spinal cord, and peripheral nerves.
Neural Probe
In an example, the recording or stimulation device can include a neural nanofabricated probe. The neural probe can include a cellular, a subcellular, or other miniature device capable of measuring a voltage signal and wirelessly transmitting the voltage signal to an intracorporeal module implanted in an accommodating structure, or capable of delivering an electrical stimulation. In an example, the intracorporeal module can be connected to a headstage or other device using wire connection, and to a data recording device using a wire or wireless connection.
In an example, the probe can separate the recording site from the transmission mechanism, which can simplify multi- structure recordings in awake, behaving animals, can enable the recording from fragile structures such
as spinal cord or peripheral nerves, and can enhance the stability of recordings in animals with thin skulls such as mice or songbirds. These advances can also make the recording device insensitive to movement of the patient, simplifying the clinical use of these devices in human patients.
Intracorporeal Communication
The following section describes intra-body (intracorporeal) communication.
Activated Iridium Oxide (a IrOx) electrodes can be implanted and sine waves transmitted from a source to a sink located some distance (such as 5 mm, 10 mm, or 15 mm) from the source. In one example, frequencies from 10Λ5 Hz to 10Λ8
Hz can be used.
In general, the brain can provide for reliable transmission of signals with little current loss up to the megahertz range. Frequencies of 100-500 kHz can be used for signals. These frequencies are high enough to not interfere with normal neuronal function, and low enough to provide reliable transmission across a greater than 1 cm range.
In certain examples, multiple access schemes for intra-brain communication, between a probe and an intracorporeal module, can be managed in a number of different ways. For example, one scheme can include frequency division multiplexing. Using this or other schemes, multiple probes can be configured to communicate simultaneously to the intracorporeal module (or to multiple intracorporeal modules) at separate frequencies. In an example,
100/200 kHz and 300/400 kHz can be used for transmit and receive for two separate probes. In other examples, other schemes, such as frequency, phase, or amplitude modulation based schemes can be used for the intra-brain communication.
Global Common Ground The following section describes a configuration and method concerning an
electrical ground for one example of recording signals without a common global ground reference potential. Typically, a body-based ground is provided by a skull screw.
In the absence of a body-based ground, at least two configurations can be used. First, the probe can be configured with three electrode sites: a differential signal between active and reference electrodes, and a larger electrode connected to amplifier isolated ground. Second, the probe can be configured with an active electrode and a reference electrode without direct connection the amplifier' s floating ground. The following section describes a configuration for transmission using separate grounds.
In one example, a signal can be transmitted (e.g., in the brain) from a transmitter to a receiver using separate grounds. Generally, a signal can be transmitted through brain tissue using current transmission (in contrast to other technologies, such as RF and induction).
In an example, two IrOx electrodes can be implanted into a brain. In this example, the first electrode serves as the source to provide a realistic simulated neural signal, and the second electrode serves as the sink to receive the transmission. The simulated neural signal provided at the source can be compared to the signal received at the sink. To ensure that ground issues were not a problem, each component (e.g., the transmitter and the receiver) can be powered by separate battery packs, each having separate grounds.
In another example, three IrOx electrodes (e.g., two transmitters and one receiver) can be implanted into a brain. In this example, the simulated neural signal and the received neural signal can be separately sent, received, and then demodulated to reconstruct the two signals. Two simulated neural signals can be taken from measured data, and each component can be powered by separate battery packs having separate grounds.
Additional Notes
The above detailed description includes references to the accompanying drawings, which form a part of the detailed description. The drawings show, by way of illustration, specific embodiments in which the invention can be
practiced. These embodiments are also referred to herein as "examples." Such examples can include elements in addition to those shown or described. However, the present inventors also contemplate examples in which only those elements shown or described are provided. Moreover, the present inventors also contemplate examples using any combination or permutation of those elements shown or described (or one or more aspects thereof), either with respect to a particular example (or one or more aspects thereof), or with respect to other examples (or one or more aspects thereof) shown or described herein.
All publications, patents, and patent documents referred to in this document are incorporated by reference herein in their entirety, as though individually incorporated by reference. In the event of inconsistent usages between this document and those documents so incorporated by reference, the usage in the incorporated reference(s) should be considered supplementary to that of this document; for irreconcilable inconsistencies, the usage in this document controls.
In this document, the terms "a" or "an" are used, as is common in patent documents, to include one or more than one, independent of any other instances or usages of "at least one" or "one or more." In this document, the term "or" is used to refer to a nonexclusive or, such that "A or B" includes "A but not B," "B but not A," and "A and B," unless otherwise indicated. In the appended claims, the terms "including" and "in which" are used as the plain-English equivalents of the respective terms "comprising" and "wherein." Also, in the following claims, the terms "including" and "comprising" are open-ended, that is, a system, device, article, or process that includes elements in addition to those listed after such a term in a claim are still deemed to fall within the scope of that claim. Moreover, in the following claims, the terms "first," "second," and "third," etc. are used merely as labels, and are not intended to impose numerical requirements on their objects.
Method examples described herein can be machine or computer- implemented at least in part. Some examples can include a computer-readable medium or machine-readable medium encoded with instructions operable to configure an electronic device to perform methods as described in the above examples. An implementation of such methods can include code, such as
microcode, assembly language code, a higher-level language code, or the like. Such code can include computer readable instructions for performing various methods. The code may form portions of computer program products. Further, the code may be tangibly stored on one or more volatile or non-volatile computer-readable media during execution or at other times. These computer- readable media may include, but are not limited to, hard disks, removable magnetic disks, removable optical disks (e.g., compact disks and digital video disks), magnetic cassettes, memory cards or sticks, random access memories (RAMs), read only memories (ROMs), and the like. The above description is intended to be illustrative, and not restrictive.
For example, the above-described examples (or one or more aspects thereof) may be used in combination with each other. Other embodiments can be used, such as by one of ordinary skill in the art upon reviewing the above description. The Abstract is provided to comply with 37 C.F.R. §1.72(b), to allow the reader to quickly ascertain the nature of the technical disclosure. It is submitted with the understanding that it will not be used to interpret or limit the scope or meaning of the claims. Also, in the above Detailed Description, various features may be grouped together to streamline the disclosure. This should not be interpreted as intending that an unclaimed disclosed feature is essential to any claim. Rather, inventive subject matter may lie in less than all features of a particular disclosed embodiment. Thus, the following claims are hereby incorporated into the Detailed Description, with each claim standing on its own as a separate embodiment. The scope of the invention should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.
Claims
1. A system comprising: a neural probe configured to detect physiological activity and to wirelessly transmit a first signal based on the physiological activity; and an intracorporeal module, communicatively coupled to the neural probe, the intracorporeal module configured to receive the first signal from the neural probe.
2. The system of claim 1, wherein the intracorporeal module is configured to transmit a second signal based on receipt of the first signal; and wherein the system includes: an external device, communicatively coupled to the intracorporeal module, the external device configured to receive the second signal from the intracorporeal module and to record data corresponding to the physiological activity.
3. The system of claim 1, wherein the physiological activity includes at least one of an intracellular signal and an extracellular signal from at least one neuron.
4. The system of claim 3, wherein the physiological activity includes an intracellular signal from a single neuron.
5. The system of claim 1, wherein the neural probe includes a plurality of neural probes, and wherein the intracorporeal module is configured to receive a plurality of first signals.
6. The system of claim 5, wherein at least two probes of the plurality of neural probes have independent electrical grounds.
7. The system of claim 1, wherein the neural probe includes: a first plurality of neural probes; and a second plurality of neural probes; wherein the intracorporeal module includes: a first intracorporeal module; and a second intracorporeal module; wherein the first plurality of neural probes is communicatively coupled to the first intracorporeal module and the second plurality of neural probes is communicatively coupled to the second intracorporeal module; and wherein the first intracorporeal module and the second intracorporeal module are communicatively coupled to the external device.
8. The system of claim 1, wherein the neural probe is configured to couple to the intracorporeal module using near field electrostatic coupling.
9. The system of claim 8, wherein the near field electrostatic coupling is isolated from normal neural activity.
10. The system of claim 1, wherein at least one of a neural probe and the intracorporeal module is configured to deliver electrical stimulation to a tissue proximate to the at least one of the neural probe and the intracorporeal module.
11. A system comprising: an implantable neural probe configured to detect brain activity and to wirelessly transmit a signal based on the detected brain activity to an intracranial module using near field electrostatic coupling; and wherein the implantable neural probe and the intra-cranial module are located proximate a neuron, and wherein the near field electrostatic coupling is independent of normal neural activity.
12. A system comprising: an implantable probe configured to detect electrical activity and to wirelessly transmit a signal based on the detected electrical activity to an intra- body module using near field electrostatic coupling; and wherein the near field electrostatic coupling is independent of normal electrical activity of the body.
13. A method comprising: detecting electrophysiological activity using an implanted probe; generating an electrical signal using the electrophysiological activity; wirelessly communicating the electrical signal to an intracorporeal module; and exchanging communications between the intracorporeal module and an external device.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10421408P | 2008-10-09 | 2008-10-09 | |
US61/104,214 | 2008-10-09 |
Publications (3)
Publication Number | Publication Date |
---|---|
WO2010042750A2 true WO2010042750A2 (en) | 2010-04-15 |
WO2010042750A3 WO2010042750A3 (en) | 2010-07-15 |
WO2010042750A8 WO2010042750A8 (en) | 2011-04-14 |
Family
ID=42101215
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2009/060048 WO2010042750A2 (en) | 2008-10-09 | 2009-10-08 | System and method for miniature wireless implantable probe |
Country Status (1)
Country | Link |
---|---|
WO (1) | WO2010042750A2 (en) |
Cited By (22)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN102304085A (en) * | 2011-07-05 | 2012-01-04 | 中国人民解放军第三军医大学第二附属医院 | Process for synthesizing trigonelline hydrochloride from dimethyl carbonate and nicotinic acid |
DE102012102710A1 (en) * | 2012-03-29 | 2013-10-02 | Jürgen Gross | Device and method for measuring electrical potentials of a living being |
WO2013188753A1 (en) * | 2012-06-15 | 2013-12-19 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
WO2015106007A1 (en) * | 2014-01-10 | 2015-07-16 | Cardiac Pacemakers, Inc. | Methods and systems for improved communication between medical devices |
WO2016118845A1 (en) * | 2015-01-23 | 2016-07-28 | Medtronic, Inc. | Implantable medical device with dual-use communication module |
US9636511B2 (en) | 2015-01-23 | 2017-05-02 | Medtronic, Inc. | Tissue conduction communication (TCC) transmission |
US9694181B2 (en) | 2012-06-15 | 2017-07-04 | Case Western Reserve University | Methods of treatment of a neurological disorder using electrical nerve conduction block |
WO2017218752A1 (en) * | 2016-06-15 | 2017-12-21 | Pluri, Inc. | Wireless biological interface platform |
US9878167B1 (en) | 2016-12-12 | 2018-01-30 | Qualcomm Incorporated | Medical implant selection protocol |
US9907496B1 (en) | 2013-06-25 | 2018-03-06 | National Technology & Engineering Solutions Of Sandia, Llc | Optoelectronic system and apparatus for connection to biological systems |
CN108365647A (en) * | 2018-02-11 | 2018-08-03 | 广东欧珀移动通信有限公司 | Control charge mode method and relevant apparatus |
US10039460B2 (en) | 2013-01-22 | 2018-08-07 | MiSleeping, Inc. | Neural activity recording apparatus and method of using same |
WO2017199052A3 (en) * | 2016-05-20 | 2018-10-04 | Imperial Innovations Limited | Implantable neural interface |
US10195434B2 (en) | 2012-06-15 | 2019-02-05 | Case Western Reserve University | Treatment of pain using electrical nerve conduction block |
US10272240B2 (en) | 2017-04-03 | 2019-04-30 | Presidio Medical, Inc. | Systems and methods for direct current nerve conduction block |
US20200281468A1 (en) * | 2017-09-29 | 2020-09-10 | University Of Strathclyde | Neural Probe Interface System and Method |
US10828485B2 (en) | 2015-10-06 | 2020-11-10 | Case Western Reserve University | High-charge capacity electrodes to deliver direct current nerve conduction block |
US10864373B2 (en) | 2015-12-15 | 2020-12-15 | Case Western Reserve University | Systems for treatment of a neurological disorder using electrical nerve conduction block |
US11376436B2 (en) | 2013-05-10 | 2022-07-05 | Case Western Reserve University | Systems and methods for preventing noise in an electric waveform for neural stimulation, block, or sensing |
US11730964B2 (en) | 2019-11-24 | 2023-08-22 | Presidio Medical, Inc. | Pulse generation and stimulation engine systems |
US11752329B2 (en) | 2018-07-01 | 2023-09-12 | Presidio Medical, Inc. | Systems and methods for nerve conduction block |
US11813459B2 (en) | 2018-02-20 | 2023-11-14 | Presidio Medical, Inc. | Methods and systems for nerve conduction block |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020116042A1 (en) * | 2001-02-20 | 2002-08-22 | Boling C. Lance | Furcated sensing and stimulation lead |
US20050090756A1 (en) * | 2003-10-23 | 2005-04-28 | Duke University | Apparatus for acquiring and transmitting neural signals and related methods |
US20060058627A1 (en) * | 2004-08-13 | 2006-03-16 | Flaherty J C | Biological interface systems with wireless connection and related methods |
-
2009
- 2009-10-08 WO PCT/US2009/060048 patent/WO2010042750A2/en active Application Filing
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020116042A1 (en) * | 2001-02-20 | 2002-08-22 | Boling C. Lance | Furcated sensing and stimulation lead |
US20050090756A1 (en) * | 2003-10-23 | 2005-04-28 | Duke University | Apparatus for acquiring and transmitting neural signals and related methods |
US20060058627A1 (en) * | 2004-08-13 | 2006-03-16 | Flaherty J C | Biological interface systems with wireless connection and related methods |
Cited By (41)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN102304085A (en) * | 2011-07-05 | 2012-01-04 | 中国人民解放军第三军医大学第二附属医院 | Process for synthesizing trigonelline hydrochloride from dimethyl carbonate and nicotinic acid |
DE102012102710A1 (en) * | 2012-03-29 | 2013-10-02 | Jürgen Gross | Device and method for measuring electrical potentials of a living being |
US11872394B2 (en) | 2012-06-15 | 2024-01-16 | Case Western Reserve Univeraity | Treatment of pain using electrical nerve conduction block |
US9387322B2 (en) | 2012-06-15 | 2016-07-12 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
US11504527B2 (en) | 2012-06-15 | 2022-11-22 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
WO2013188753A1 (en) * | 2012-06-15 | 2013-12-19 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
US9694181B2 (en) | 2012-06-15 | 2017-07-04 | Case Western Reserve University | Methods of treatment of a neurological disorder using electrical nerve conduction block |
US11318300B2 (en) | 2012-06-15 | 2022-05-03 | Case Western Reserve University | Treatment of pain using electrical nerve conduction block |
US11033734B2 (en) | 2012-06-15 | 2021-06-15 | Case Western Reserve University | Treatment of pain using electrical nerve conduction block |
EP3572121A1 (en) * | 2012-06-15 | 2019-11-27 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
US9889291B2 (en) | 2012-06-15 | 2018-02-13 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
US10441782B2 (en) | 2012-06-15 | 2019-10-15 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
US10195434B2 (en) | 2012-06-15 | 2019-02-05 | Case Western Reserve University | Treatment of pain using electrical nerve conduction block |
US10071241B2 (en) | 2012-06-15 | 2018-09-11 | Case Western Reserve University | Therapy delivery devices and methods for non-damaging neural tissue conduction block |
US10039460B2 (en) | 2013-01-22 | 2018-08-07 | MiSleeping, Inc. | Neural activity recording apparatus and method of using same |
US11376436B2 (en) | 2013-05-10 | 2022-07-05 | Case Western Reserve University | Systems and methods for preventing noise in an electric waveform for neural stimulation, block, or sensing |
US11786733B2 (en) | 2013-05-10 | 2023-10-17 | Case Western Reserve University | Systems and methods for preventing noise in an electric waveform for neural stimulation, block, or sensing |
US9907496B1 (en) | 2013-06-25 | 2018-03-06 | National Technology & Engineering Solutions Of Sandia, Llc | Optoelectronic system and apparatus for connection to biological systems |
EP3308833A1 (en) * | 2014-01-10 | 2018-04-18 | Cardiac Pacemakers, Inc. | Methods and systems for improved communication between medical devices |
WO2015106007A1 (en) * | 2014-01-10 | 2015-07-16 | Cardiac Pacemakers, Inc. | Methods and systems for improved communication between medical devices |
US10561850B2 (en) | 2015-01-23 | 2020-02-18 | Medtronic, Inc. | Implantable medical device with dual-use communication module |
US9636511B2 (en) | 2015-01-23 | 2017-05-02 | Medtronic, Inc. | Tissue conduction communication (TCC) transmission |
WO2016118845A1 (en) * | 2015-01-23 | 2016-07-28 | Medtronic, Inc. | Implantable medical device with dual-use communication module |
US9808632B2 (en) | 2015-01-23 | 2017-11-07 | Medtronic, Inc. | Implantable medical device with dual-use communication module |
US10828485B2 (en) | 2015-10-06 | 2020-11-10 | Case Western Reserve University | High-charge capacity electrodes to deliver direct current nerve conduction block |
US11779762B2 (en) | 2015-12-15 | 2023-10-10 | Case Western Reserve University | Systems for treatment of a neurological disorder using electrical nerve conduction block |
US10864373B2 (en) | 2015-12-15 | 2020-12-15 | Case Western Reserve University | Systems for treatment of a neurological disorder using electrical nerve conduction block |
WO2017199052A3 (en) * | 2016-05-20 | 2018-10-04 | Imperial Innovations Limited | Implantable neural interface |
EP3777965A1 (en) * | 2016-05-20 | 2021-02-17 | Imperial College Innovations Limited | Implantable neural interface |
US11589790B2 (en) | 2016-05-20 | 2023-02-28 | Imperial College Innovations Limited | Implantable neural interface |
WO2017218752A1 (en) * | 2016-06-15 | 2017-12-21 | Pluri, Inc. | Wireless biological interface platform |
US9878167B1 (en) | 2016-12-12 | 2018-01-30 | Qualcomm Incorporated | Medical implant selection protocol |
US11027126B2 (en) | 2017-04-03 | 2021-06-08 | Presidio Medical, Inc. | Systems and methods for direct current nerve conduction block |
US10272240B2 (en) | 2017-04-03 | 2019-04-30 | Presidio Medical, Inc. | Systems and methods for direct current nerve conduction block |
US11918803B2 (en) | 2017-04-03 | 2024-03-05 | Presidio Medical, Inc. | Systems and methods for direct current nerve conduction block |
US11596304B2 (en) * | 2017-09-29 | 2023-03-07 | University Of Strathclyde | Neural probe interface system and method |
US20200281468A1 (en) * | 2017-09-29 | 2020-09-10 | University Of Strathclyde | Neural Probe Interface System and Method |
CN108365647A (en) * | 2018-02-11 | 2018-08-03 | 广东欧珀移动通信有限公司 | Control charge mode method and relevant apparatus |
US11813459B2 (en) | 2018-02-20 | 2023-11-14 | Presidio Medical, Inc. | Methods and systems for nerve conduction block |
US11752329B2 (en) | 2018-07-01 | 2023-09-12 | Presidio Medical, Inc. | Systems and methods for nerve conduction block |
US11730964B2 (en) | 2019-11-24 | 2023-08-22 | Presidio Medical, Inc. | Pulse generation and stimulation engine systems |
Also Published As
Publication number | Publication date |
---|---|
WO2010042750A8 (en) | 2011-04-14 |
WO2010042750A3 (en) | 2010-07-15 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
WO2010042750A2 (en) | System and method for miniature wireless implantable probe | |
Chen et al. | A wireless millimetric magnetoelectric implant for the endovascular stimulation of peripheral nerves | |
US9854987B2 (en) | Distributed, minimally-invasive neural interface for wireless epidural recording | |
KR102013463B1 (en) | Implantable wireless neural device | |
US7991475B1 (en) | High density micromachined electrode arrays useable for auditory nerve implants and related methods | |
US9949376B2 (en) | Cortical implant system for brain stimulation and recording | |
Ha et al. | Silicon-integrated high-density electrocortical interfaces | |
Ahmadi et al. | Towards a distributed, chronically-implantable neural interface | |
Mestais et al. | WIMAGINE: wireless 64-channel ECoG recording implant for long term clinical applications | |
US9061134B2 (en) | Systems and methods for flexible electrodes | |
EP2709716B1 (en) | Cortical interface with an electrode array divided into separate fingers and/or with a wireless transceiver | |
US20100265680A1 (en) | Pocket-enabled chip assembly for implantable devices | |
US20230165499A1 (en) | Implantable neural interface | |
WO2010056438A2 (en) | Shielded stimulation and sensing system and method | |
US20120123289A1 (en) | System and method for wireless transmission of neural data | |
JP7307738B2 (en) | Monolithic neural interface system | |
US20210007602A1 (en) | Brain implant with subcutaneous wireless relay and external wearable communication and power device | |
WO2016187254A1 (en) | Chiplet based wireless intranet for very large scale recordiing and stimulation | |
CN116648284B (en) | Implantable neurophysiologic device | |
Akin | An integrated telemetric multichannel sieve electrode for nerve regeneration applications | |
Patrick | Design, fabrication, and characterization of microelectrodes for brain-machine interfaces | |
Tripathi et al. | Low power electrode interface for implantable medical devices | |
Yu | Magnetoelectric Wireless Power and Data Links for Millimetric Bioelectronic Implants | |
WO2024097404A1 (en) | Implantable and flexible cmos recording and stimulating device which includes one or more neural electrode arrays | |
WO2020225780A1 (en) | An electrical stimulation device with synchronized pulsed energy transfer |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 09819905 Country of ref document: EP Kind code of ref document: A2 |
|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
122 | Ep: pct application non-entry in european phase |
Ref document number: 09819905 Country of ref document: EP Kind code of ref document: A2 |