WO2024079699A1 - Réseaux de micro-électrodes pour interfaçage électrique - Google Patents

Réseaux de micro-électrodes pour interfaçage électrique Download PDF

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Publication number
WO2024079699A1
WO2024079699A1 PCT/IB2023/060324 IB2023060324W WO2024079699A1 WO 2024079699 A1 WO2024079699 A1 WO 2024079699A1 IB 2023060324 W IB2023060324 W IB 2023060324W WO 2024079699 A1 WO2024079699 A1 WO 2024079699A1
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Prior art keywords
electrode array
well
wells
cells
tissue
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PCT/IB2023/060324
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English (en)
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Yi Guo
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Neural Automations Ltd.
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Publication of WO2024079699A1 publication Critical patent/WO2024079699A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—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
    • A61N1/0531—Brain cortex electrodes
    • 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
    • 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
    • A61B5/24—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
    • A61B5/294—Bioelectric electrodes therefor specially adapted for particular uses for nerve conduction study [NCS]
    • 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
    • A61N1/0551—Spinal or peripheral nerve electrodes
    • 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
    • A61N1/0551—Spinal or peripheral nerve electrodes
    • A61N1/0553—Paddle shaped electrodes, e.g. for laminotomy

Definitions

  • the devices have a micro-electrode array configuration with grafted cells reliably positioned within the array that are capable of electrical connection with tissue adjacent to the device.
  • organ-on-a-chip devices incorporate living cells to achieve in-vitro simulation of physiology, those devices are not intended for and have important differences with a device the electrically interface with biological tissue in a highly specific manner.
  • organ-on-a-chip devices incorporate living cells to achieve in-vitro simulation of physiology, those devices are not intended for and have important differences with a device the electrically interface with biological tissue in a highly specific manner.
  • 2730645A2 titled “Organ-on-a-chip-device” is to establish or maintain organs or organoids as well as various cell niches.
  • Electrode arrays are a critical physical component of electrical interfaces with biological tissue that allows researchers to collect electric activity from nervous systems and stimulate activity in them.
  • Three main types of commercially-available electrode arrays are: Surface Arrays (NeuroNexus), Utah Electrode Array (The University of Utah), Wire (Neuralink Corp.). All those devices, however, have poor specificity. This arises from the nature of electric fields in conductive medium, which spread by ionic gradient and the fact that electric field strength declines approximately proportionally with the distance.
  • Stimulation is equally problematic, as a pulse at an electrode could activate dozens to hundreds of cells in a diffuse manner. This occurs regardless of manufacturing precision.
  • microfabrication techniques can produce contacts 10 nm apart, those contacts continue to individually pick up activity from hundreds to thousands of cells.
  • the density of neurons on the surface of rat visual cortex is estimated to be in the range of 70,000/mm 3 [4] and electric field from each cell can spread over hundreds of microns.
  • thermal- optical stimulation [5], ultrasonic stimulation [6], and trans-cranial magnetic stimulation [7] attempts to trigger activity in neurons through intervening tissues.
  • thermal- optical stimulation [5], ultrasonic stimulation [6], and trans-cranial magnetic stimulation [7] attempts to trigger activity in neurons through intervening tissues.
  • the precision of those devices are inherently limited because: (1) the skull is a very good low-pass filter. (2) Relative biological motion between energy source and target tissue. (3) Many of them rely on slow actuation mechanism like thermal energy transfer.
  • those devices are limited in that they cannot record simultaneously while stimulating. The second and the last point also apply to infrared thermal-optical stimulation even through it can to be relatively precise when applied directly to the brain via optic fibers.
  • EEG EEG and Functional MRI
  • Resolution tend to be comparatively poor: EEG uses large macro electrodes that sample activity over entire section of the skull.
  • fMRI has lower resolution than normal MRI, with spatial resolution of 0.75-0.5mm achieved only in extremely strong magnetic fields [8], [9], Temporal resolution is in the order of seconds.
  • fMRI requires the subject to be stationary and so is not compatible with behavior experiments. Neither of those techniques can be used for stimulation.
  • Electrocorticography is similar to EEG but places electrodes on the surface of the brain instead of the top of the scalp. It’s often used to locate focus of epileptic seizures. ECOG usually use macro electrodes, unless a flexible array is used (see Flexible Surface Array). Resolution is higher than EEG, but still relatively low and more suited for “bulk” interfacing, especially when compared to the micro-electrode arrays described and claimed herein.
  • Another conventional device is a glass micro-electrode array, such as a Silver / Silver Chloride (Ag/AgCl) electrode and/or gold or titanium contacts built onto a glass substrate by surface micro-machining (Multi Channel Systems MCS GmbH (a divisional of Harvard Bioscience, Inc.). Those devices are used only for in vitro studies as their size and rigidity make them impractical as an implantable devices.
  • a glass micro-electrode array such as a Silver / Silver Chloride (Ag/AgCl) electrode and/or gold or titanium contacts built onto a glass substrate by surface micro-machining (Multi Channel Systems MCS GmbH (a divisional of Harvard Bioscience, Inc.).
  • Those devices are used only for in vitro studies as their size and rigidity make them impractical as an implantable devices.
  • Other devices include flexible surface arrays that combine characteristics of ECoG and Glass electrode. They are generally a grid of micro-electrode (usually PEDOT:PSS) built onto the surface of a Parylene film by surface micro-machining. Surface electrodes are less rigid then penetrating arrays (see Utah Array), and thus develop less mechanical problems. Those devices are usually placed on the surface of the brain, and have relatively good resolution. However, the specificity remains poor because electric field from multiple neurons overlap. Accordingly, there remains a problem in the art with respect to achieving specificity (e.g., a more one-to-one device to biological cell electrical interconnection), regardless of the underlying manufacturing precision or resolution.
  • specificity e.g., a more one-to-one device to biological cell electrical interconnection
  • the Utah Array first developed by University of Utah, is comprised of grids of penetrating microneedles on top of a rigid silicon substrate which contains electrical interconnects. Each microneedle contains multiple Ag/AgCl electrodes along its length. Those electrodes are good at sampling signals from deep layers of the brain. They tend to have high precision, and can sometimes achieve good specificity. For example, it is possible to slowly drive a Utah electrode into the brain while listening for spike trains recorded when a needle penetrate into a cell. While excellent for acute studies, Utah electrodes cause neural tissue damage, including over the long term. The brain is in constant biological motion, including due to breathing, body movement, respiration and blood flow. Because the Utah array is rigid, the relative mechanical differences causes constant force mismatch and abrasion around the array. This in turn triggers tissue reaction, resulting in the electrode being gradually encased in layers of scar tissue, increasing impedance and eventually rendering the device useless.
  • Microwire based devices utilize wire electrodes formed from electrically-insulated microscopic silver wires with insulation stripped at the tip. They are individually inserted into the brain either manually or by a robotic device (Neuralink Corp., Fremont, CA). While soft at the macroscopic level, those wires are nevertheless rigid enough to penetrate small distances. Both resolution and precision are limited with the manual method, because it is physically challenging to control and maneuver wires precisely, including in a biological tissue. This may have been improved by robotic devices since, given the presentation by Neuralink Corp. [12]
  • Examples of existing electrode interfaces include the Utah array (see, e.g., www.sci.utah.edu/ ⁇ gk/abstracts/bisti03/), surface/flexible array (see, e.g., www.multichannelsystems.com/products/flexmea36), and glass array (see, e.g., www.multichannelsy stems. com/products/60pedotmea20030ir-au-gr).
  • the specificity problem described above is addressed herein via a novel microfabricated electrode array which uses living cells to form contacts, and more specifically electrical contacts including synaptic contacts, between conducting polymer electrodes and target biological tissue, including neural tissue. Through that physical contact, specific electrical interfacing is achieved.
  • the devices provided herein comprise a flexible micro fabricated device made from a polymer, such as PDMS (polydimethylsiloxane) punctuated by a regular grid of wells.
  • the polymer may be on the order of 1 mm thick, such as between about 100 pm and 2 mm thick, depending on the operating conditions and application of interest, including the electric field spread into the well.
  • Conductive polymer contacts are positioned within a well on a surface location, including located at the bottom of the wells.
  • the other top end of the well is open. Neurons are introduced into the wells and cultured, including with hydro-gels, to guide sprouted axons and dendrites towards the open end of the wells. Those sprouted axons and dendrites are available to make physical contact with target neural tissue.
  • the combination of the precisely located sprouted axons, their one-to-one contact and electrical interconnection with biological tissue, and the special electrical grounding of the device surface facing the biological tissue provides the device with the benefit of high specificity in combination with high resolution and attendant functional benefit, including: the ability to precisely, reliably and continuously electrically interface with biological tissue without damage or trauma, including down to a very small sub-regions, with each sub-region specific to an underlying electrical connection defined by a single well.
  • Electrodes with grafted neuronal cells configured to establish a biological electrical connection between the grafted neuronal cell and a target neuronal cell in a biological tissue in which the electrode is positioned. In this manner, substantially all electrical connection between the electrode and the biological tissue is through the biological electrical connection.
  • the electrically conducting material of the electrode has an outer surface, wherein the outer surface is optionally formed of an outer material that is different from a core material of the electrically conducting material, with at least one neuronal cell grafted to the outer surface of the electrically conducting material.
  • cellular electrodes including in the form of cellular electrode arrays, and related methods of making and methods of using any of the cellular electrode arrays to electrically interface with biological tissue and for making any of the cellular electrode arrays.
  • a cellular electrode array comprising a flexible polymer substrate having a top surface and an array of wells disposed in the flexible polymer substrate. Each well has an inner-facing surface that defines a well volume.
  • the inner facing surface may comprise a bottom surface and side wall surfaces that extend from the bottom surface to the flexible polymer substrate top surface.
  • a conductive contact such as a conductive polymer contact or a AgCl contact, at least partially covers the well inner-facing surface, such as positioned at the bottom surface and/or around at least a portion of the side wall.
  • the conductive contact is a conductive polymer contact, although other electrically-conductive materials are compatible with the electrode arrays, particularly materials that are flexible and are not rigid, so as to not adversely impact the overall device conformability to the biological tissue. In this manner, a well depth corresponding to a distance between the flexible polymer substrate top surface and the well bottom surface is defined.
  • the well volume may be characterized in terms of the volume, and for a circular well cross-section the volume may be calculated as Hur 2 (equation (1)), with H the well depth and r the effective radius of the well, such as d/2, with d the effective diameter of the well.
  • Hur 2 equation (1)
  • H the well depth
  • r the effective radius of the well
  • d the effective diameter of the well.
  • the invention is compatible with any of a range of well cross-sections, including non-circular cross-sections such as ovals, rectangular, square and the like.
  • Wells may have shapes with non-constant cross sections, such as tapers and funnels, including so as to receive a droplet.
  • the well volume can be between 1 pL and 2 mL, including between 10 pL and 1 mL.
  • the well may be configured to contain a hydrogel in each well and to receive a neuronal cell.
  • the hydrogel facilitates directed growth of sprouted axons and dendrites from the neuronal cell in a direction toward the flexible polymer substrate top surface.
  • the ends of the sprouted axons and dendrites are available to physically contact biological cells, including biological cells that are electrically active, generating and/or responding to electric stimuli or field.
  • the conductive polymer contact may be positioned at the well bottom surface and/or along sidewalls and portions thereof.
  • the polymer substrate that is flexible facilitates conformal contact with a biological tissue, including a biological tissue that is curved or has a time-varying surface shape.
  • the cellular electrode is configured to operably connect flush against a tissue surface, including a tissue that corresponds to a brain surface with the operably connected mediated by synaptic connections between the neuronal cells in the wells (e.g., “grafted neuronal cell) and dendrites in the biological tissue, including dendrites from brain adjacent to the brain surface for biological tissue that is brain.
  • grafted in the instant context refers to the neuronal cell that is reliably supported by wells such that there is sufficient proximity to an electrode surface that there is the ability of each of the grafted neuron and the electrode to electrically influence each other’s electric field.
  • Each well may have a well depth that is between 10 pm and 2 mm.
  • Each well may have a volume that is between 10 pL and 1 mL.
  • Each well may have a characteristic diameter of between 1 pm and 1 mm.
  • the volume of the well may be converted into a characteristic diameter if the well depth is known via equation (1).
  • the cellular electrode array may have a well density of between 0.001 wells/pm 2 (1000 wells/mm 2 ) to 0.1 wells/pm 2 (10 5 wells/mm 2 ).
  • Adjacent wells may be separated by a separation distance of between 10 pm and 1 mm.
  • the resolution of the device may be controlled via well density and/or well spacing, depending on the application of interest.
  • the specific connection between the grafted cells in the wells to the corresponding tissue provides the high specificity.
  • the well density may be constant or may spatially vary, with certain sub-regions of the device having a higher resolution than others. For example, the central 50%-75% of the device may have a higher well density than the outer perimeter area of the device.
  • the polymer substrate may be conformable, so that it conforms to an irregularly- shaped tissue surface without adversely impacting device functionality.
  • the conformability may be described in terms of macroscopic and/or microscopic adaptations to the curvature of the tissue surface, with the adaptations ensuring there can be reliable electrical connection between the grafted cell and the biological tissue. This conformability can be important because if the separation distance is too great, there simply will be too great a distance to span for electrical connections to be established and/or maintained.
  • the conductive polymer may have a range of thicknesses and/or a range of layer numbers. For example, there may be a grounding layer and/or electrical contact layer. The layer thickness may be between 1 pm and 100 pm. Optionally, the conductive polymer layer has a thickness that is less than the substrate thickness or well depth.
  • the non-conductive PDMS layer on the conductive PDMS layer forms an insulated conductive layer that is an electrical interconnect between the electrodes and external electronic components, such as amplifiers, cables, or PCBs, and to controllers, computers, and the like.
  • external electronic components is used broadly herein. They also include, but are not limited to, contact pads on the other side of the array which in turn connect to other external electronic components (e.g., to facilitate reading a signal out of the array).
  • On-board amplifiers may also be characterized as an external electronic component.
  • the conductive PDMS layer can be a PDMS composite layer.
  • the electrical connection with the grafted neuronal cell need not be a physical connection, but instead the grafted neuronal cell, due to its proximity with the electrode (including electrically-active material such as conductive contact), facilitates the ability to detect an electric field projected by the grafted neuron, and similarly influence the electric field around the grafted neuron.
  • the flexible polymer substrate may be formed of polydimethylsiloxane (PDMS), including layers of PDMS for insulative and/or electrical conductance properties.
  • PDMS polydimethylsiloxane
  • a conducting layer of PDMS may be formed from a composite, such as PDMS spiked with an electrically conductive material to ensure current may travel through the PDMS composite conductive layer.
  • the non-conductive PDMS layer may comprise a spin coated layer on the conductive layer to form an insulation layer having an interconnect passage for receiving an interconnect to electrically contact for the conductive PDMS layer.
  • the cellular electrode array may comprise at least two non-conductive PDMS layers, including at least three, and may have any of a range of conductive and non- conductive PDMS layers.
  • the cellular electrode array may further comprise neuronal cells positioned in the wells, including grafted onto the conductive polymer contact.
  • Microfluidics may be employed to reliably deposit a desired number of cells into each well, such as ranging from between 1 and 10 cells, 1 and 5 cells, and about 1 cell per well.
  • the neuronal cells may be selected to synaptically connect to a subject during use, and may further be selected to be immune compatible with a subject for in vivo use.
  • any of the cellular electrode arrays may have a top surface of the flexible polymer that is functionally an electrical conductor so as to ground the cellular electrode array. In this manner, during use electrical communication between the cellular electrode array and a subject is confined to the neuronal cells in the wells synaptically connected to the subject (in vivo) or to a volume of an explanted tissue (in vitro or ex vivo).
  • the grounding layer instead of a simple grounding layer covering the entirety of the top surface, the grounding layer cover only part of the top surface.
  • a conventional surface having a micro-electrode array may be provided onto the part of the remaining top surface for simultaneous collection non-specific electric field activity. This configuration can be useful for debugging or to serve as a backup.
  • the cellular electrode array may have a device footprint of up to 1000 mm 2 , and optionally with up to 10,000 unique contacts between the neuronal cells in the wells and a tissue in which the cellular electrode array is implanted.
  • the cellular electrode arrays provided herein are compatible with any of a range of footprint sizes, depending on the application of interest, along with any number of wells with a range of well density.
  • One of ordinary skill in the art can select the appropriate well density based on the desired degree of actuation control and/or measurement resolution.
  • the method may comprise the steps of: grafting a neuronal cell in at least a portion of, or each of, the wells of the cellular electrode array (or to an electrode outer surface for the more general electrode configuration).
  • the cellular electrode array (or the electrode for the more general electrode configuration) with the grafted neuronal cells is contacted with the biological tissue.
  • the electrode array may be positioned such that the top surface of the substrate contacts the biological tissue so that the sprouted dendrites and/or axons that extend out toward or past the well can also contact the biological tissue.
  • the grafted neuronal cells are electrically connected to biological cells adjacent to the grafted neuronal cells, thereby forming electrical contacts between the biological tissue and the cellular electrode array.
  • the biological tissue can then be electrically interfaced via the grafted neuronal cells that are in electrical contact with the biological tissue. Similar interactions occurs for the more general electrode configuration.
  • the electrical interfacing may comprise electrically actuating the biological tissue and/or measuring an electrical parameter of the biological tissue.
  • the electrically interfacing step may comprise measuring current flowing to or from at least a portion of the grafted neuronal cells that are electrically connected to biological tissue.
  • the electrical interfacing may comprise generating a map of electric potential over the interfaced area, corresponding to a portion or all of the electrode array footprint. Such a map, because of the high specificity of electrical interfacing between biological tissue and the array via the grafted neurons, will have very high spatial resolution with the measured electric potential measured at each well position of high accuracy and sensitivity as the measured electric potential is specific to that location with minimal crosstalk from non-adjacent regions of biological tissue.
  • the interfacing may also utilize statistical methods for teasing out the measured action potentials from a bulk signal being detected by the electrode through a path independent of the grafted cell.
  • the electrical interfacing step may comprise, as desired, collection of bulk signals mixed with specific signals, such as signals via the biological electrical connection, such as action potentials. Subsequently instead of discarding such bulk signals as noise, statistically separating the bulk from the specific signals, using techniques such as PCA, ICA, frequency domain filtering or any other technique that exploit the characteristics of action potentials or spike trains.
  • specific signals such as signals via the biological electrical connection, such as action potentials.
  • statistically separating the bulk from the specific signals using techniques such as PCA, ICA, frequency domain filtering or any other technique that exploit the characteristics of action potentials or spike trains.
  • the method may further comprise the steps of: selecting a portion of the wells having neuronal cells electrically connected to biological cells and electrically interfacing the selected portion of the wells with the biological cells.
  • the selected portion of wells may correspond to a spatial region having a surface area of between 1 pm 2 and 5 mm 2 .
  • the method may further comprise the step of matching a mechanical property of the cellular electrode array with a mechanical property of the biological tissue.
  • the mechanical property may be a modulus, such as a Young’s modulus, that is within 50%, 20% or 10% of each other.
  • the arrays provided herein are compatible with any of a range of biological tissue, including biological tissue where electric potential and electrical activation are of importance.
  • the biological tissue may be selected from the group consisting of: brain, spinal cord, peripheral nerves, a three-dimensional cell culture (including a bioartificial organ), and organotypic cultures.
  • Particularly useful is brain tissue, where the brain tissue comprises neuronal cells with brain dendrites that are capable of synaptically connecting to the grafted neuronal cells of the array, thereby providing the specific and reliable electrical connection between the electrodes of the array and the brain tissue.
  • the method may comprise the steps of: forming a recessed master comprising an array of relief features on a silicon wafer surface or SU8.
  • the relief features may correspond to the desired array of wells size, location and geometry.
  • a polymer layer is cast against the array of relief features and the cast polymer layer cured.
  • the cured polymer layer is patterned to expose a top portion of the relief features.
  • Electrode contacts are deposited onto the exposed top portion of the relief features and an insulating layer deposited over the deposited electrode contacts.
  • the electrode contacts are electrically interconnected for electrical connection to a to an electrical component, including one or more of an amplifier, a printed circuit board (PCB), a transmitter, an analog filter, and/or an analog to digital converter (ADC) or any component useful for connecting or communicating directly or indirectly with an electronic device, such as a computer.
  • the silicon wafer is removed from the cast polymer and other layers, thereby making the cellular electrode array having an array of wells, with the wells corresponding to the array of relief features.
  • the patterning may comprise removal (e.g., etching) and/or addition (e.g., deposition) including by selective curing.
  • the forming the recessed master may comprises processing the master silicon wafer surface by: reactive ion etching; and/or cutting with a die saw.
  • the casting step may comprise: casting a main body layer of PDMS to cover the exposed relief features on the master, wherein the main body layer of PDMS is not electrically conductive.
  • Conductive paths are patterned onto the main body in conductive PDMS composite by etching, lift-off or selective curing.
  • Grounding layer can be created separately by spin coating on another wafer and attached to the main body by adhesion or transfer printing after the main body is removed from the master.
  • the method may further comprise the step of re-using the recessed master to make another cellular electrode array. In this manner, cost savings may be realized.
  • the method may further comprise the steps of: providing neuronal cells to the wells; providing a hydrogel, including a collagen solution, to the wells; culturing the neuronal cells to generate axon and dendrite growth. In this manner, the array is ready for contact with a biological tissue. Accordingly, the method may further comprise the step of contacting the cellular electrode array with a biological tissue so that the neuronal cells electrically interface with the biological tissue, including biological cells within the biological tissue.
  • the method may be practiced on the living body, including a human or a non-human animal. The method may be in vivo, in vitro or ex vivo.
  • FIGs. 1A-1C Schematic illustration of the cellular electrode array, with a side view (FIG. 1A), a top view (FIG. IB) and an implanted view with attendant electronics for measuring a signal output (FIG. 1C).
  • FIGs. 2A-2E manufacturing steps for an electrode-neuron grafted array.
  • FIG. 3 is a flow-chart schematic of certain relevant manufacturing steps for making the electrode array.
  • Dark solid is SU8; light solid is PDMS; left hatching represents a conductive composite; right hatching represent wells and holes; horizontal hatching represents metallization; vertical hatching represents channels.
  • FIG. 4 is similar to FIG. 3, but provides another embodiment of selected manufacturing steps for making the electrode array.
  • FIG. 5 is a schematic of the electrode in use to form a biological electrical connection with a target cell via a grafted neuronal cell.
  • Interfacing is used herein to refer to the ability of two materials or components to electrically interact with each other, so that a change in an electrical parameter (e.g., potential) of one material or component affects the state or status of another material or component, without adversely impacting the functionality of each material or component.
  • Interfacing is used broadly herein to include electrical stimulation (e.g., “actuation”) and/or electric parameter detection (e.g., “measurement” or “detection”).
  • the arrays provided herein may electrically stimulate biological cells and/or detect an electrical field or electrical parameter (potential, current) generated by biological cells.
  • Flexible refers to the ability of a material, structure, device or device component to be deformed into a curved shape without undergoing a transformation that introduces significant force that would otherwise result in failure.
  • a flexible material, structure, or device may be deformed into a curved shape without introducing a force greater than the failure point of the material.
  • Conductive polymer composite refers to a polymer that is capable of conducting an electric charge.
  • the conductive polymer contact may be formed from a composite material, including a mixture of several polymers and a mixture of polymer with distributed metallic elements.
  • operably connected refers to a configuration of elements, wherein an action or reaction of one element affects another element, but in a manner that preserves each element’s functionality.
  • a cellular electrode array in operable connection with the biological tissue or surface refers to the ability of the electrode array to electrically interface with the tissue, including cells, without adversely impacting the tissue or the array.
  • Electrode refers to the component of the cellular electrode array that can be electrically energized to electrically stimulate a biological material and/or to detect an electrical parameter arising from the biological material.
  • the electrode may be a conducting metal.
  • the electrode may be a composite, with a core material that is covered or coated by an outer material that is different from the core material.
  • the outer material may correspond to coatings of active sites where electrical connection is desired.
  • the electrode may be coated in Poly(ethylenedioxythiophene) (PEDOT).
  • PEDOT Poly(ethylenedioxythiophene)
  • the electrode may be configured to graft to a neuronal cell, so that substantially all of the electrical connection with a biological tissue is via the grafted neuronal cell(s).
  • substantially all refers to at least 80%, at least 90%, or at least 95% of electrical current that travels between the biological tissue and the electrode via the grafted neuronal cell. “Substantially all” also refers to the situation where electrical signals in the form of action potentials are provided between the electrode and the biological tissue without loss or substantial degradation of the action potentials, including the frequency of action potentials.
  • Device footprint refers to the surface area defined by the perimeter of the polymer substrate.
  • adjacent refers to biological tissue that is sufficiently close to the grafted cells in the wells of the electrode array is able to make electrical contact with the tissue, including biological cells of the tissue.
  • the term is intended to reflect that there is a constrained region of contact, as the grafted cells have a spatial limit as to how far from the well in which they are contained can establish direct electrical contact. At least part of the constraint is the distance from the well the sprouted dendrite or axon can grow.
  • adjacent includes a functional definition based on typical maximum axon length is less than 100 pm, including between about 20 pm and 60 pm. In one aspect, any tissue that is within 100 pm from a reference location, such as an edge of a well, is considered to be “adjacent” to that reference location.
  • Bulk electrical interfacing refers to an electrical interface with electrodes on the surface of the device, where an electrical parameter (e.g., electrical potential) or electrical signal (e.g., current or potential) is measured or provided directly with the electrodes without the biological/synaptic connection.
  • an electrical parameter e.g., electrical potential
  • electrical signal e.g., current or potential
  • “Well” is used broadly herein to refer to a volume in a flexible polymer substrate that can reliably support growth of a biological cell under culture conditions.
  • the well may have any of a range of shapes.
  • the cross-sectional shape may be uniform, such as cylindrical in nature.
  • the wall may have a funnel or taper shape, with a larger cross-sectional area toward the flexible polymer substrate top surface, tapering to a minimum cross-sectional area in a direction away from the top surface.
  • the well can be shaped depending on the application of interest. For example, to receive a droplet containing very few neuronal cells (e.g., down to about 1 neuronal cell/droplet), the well may have a tapered configuration to help guide and confine the droplet to the well.
  • Example 1 Device Overview
  • a cellular electrode array 1 is formed from a flexible polymer substrate 10 having a top surface 20 and an array of wells 30.
  • Each well has an inner facing surface 40, including a bottom surface, and a conductive polymer contact 50 (illustrated as positioned to form the bottom surface).
  • a non-conductive PDMS layer and a conductive polymer layer can effectively form an insulated conductive layer that is functionally an electrical interconnect between the conductive polymer contact 50 and an external electronic component 51.
  • Well depth is illustrated by arrow 60.
  • a hydrogel 70 can be disposed in each well.
  • one neuronal 80 with sprouted axon and dendrite 90 is illustrated per each well, available for contact with a biological tissue 100.
  • FIG. 1A is a side cross-section and FIG. IB atop view that also illustrates conductive top surface 20.
  • FIG. 1C illustrates the cellular electrode array 1 implanted under the skull and electrically interfacing with biological tissue that is brain. For simplicity, the interface is shown in the direction of detecting a signal.
  • the signal may be generated by the device and used to actuate biological tissue. Both the detecting and generated signal may be spatially varying over the footprint area (see, e.g., FIG. IB showing the footprint of a 4x3 electrode array).
  • an electrode 500 (which can, functionally, be equivalent to conductive polymer contact 50 of FIG. 1A-1C, including by being formed of a plurality of PDMS layers 501) formed of an electrically conducting material 510 having an outer surface 520.
  • the electrode may be formed of a plurality of distinct materials, such as an outer material 530 that is different from a core material 540 (e.g., the inner body) of the electrode.
  • Line 505 represents system boundary, such as the implanted portion footprint.
  • a neuronal cell 550 is electrically connected to the electrode, as represented by the two-way electrical current arrows 560. In this manner, neuronal cell 550 is characterized as a “grafted” neuronal cell with respect to the electrode 500.
  • the grafted neuronal cell 550 has a biological electrical connection 580. This is reflected by the two-way arrows 585, indicating that the electrode may be used to stimulate target 570 or to detect an electrical parameter of target 570.
  • Arrows with strikethrough 590 corresponds to leakage of electric current between biological tissue and electrode, reflecting that substantially all electrical connection is between the biological electrical connection 580 with attendant arrows 560 rather than “non-specific” electrical connection of electrical path 590. For example, at least 80% of the electrical current may be via path 560 compared to the non-specific path 590.
  • Example 2 Summary of method of making the device
  • FIGs. 2A - 2E are summaries of various steps that can be utilized to make an electrode-neuron grafted array. Unless noted otherwise, dimensions are only exemplary.
  • FIG. 2A illustrates multiple potential devices on one wafer. For simplicity, subsequent figures illustrate one device. All units are in mm. The designs and dimensions shown are a representative embodiment. Step nos. refer to the steps further explained in Example 3.
  • FIG. 2A illustrates an initial step with intersecting grooves cut into the surface of the wafer with a diamond saw. An 8 by 8 well design is shown as an example, actual well density can be much higher.
  • FIG. 2B illustrates second step described in step 1.b)ii below, isotropic wet etching creates rounded profdes.
  • the profde created using l.b)i will be similar, except missing rounds near the apex and the bases of the columns. Either process is acceptable.
  • FIG. 2C illustrates casting of the Device Body described in step 3.
  • the thin layer of conductive PDMS (10 pm in this example) serves as the ground and can be deposited before the main body or attached as the final step.
  • the main body should exceed the top of the columns by a known amount.
  • FIG. 2D illustrates deposition of electrodes and part of the interconnects after steps 4. a), 4.b) and 4.c).
  • Device Body should be etched to the top of the master, then conductive PDSM is patterned by selective curing (if photo-reactive) or by etching with a metallic mask layer (if not photo-reactive). Wiring is optimized by any number of techniques and processes, including but not limited to manual determination and/or using electronic design automation (EDA) software for large arrays. Note some electrodes are not connected to contact pads in this layer because multiple layers are used for dense arrays.
  • EDA electronic design automation
  • FIG. 2E illustrates the completed electronics after step 4.
  • Electrical interconnects 200 may not all fit in the same layer on a dense electrode.
  • the interconnects 200 electrically connect the electrodes to the contact pads at or toward the device edges. Interconnects connecting to various regions of electrodes may be at different layers in the device. For example, the interconnects that electrically contact the electrodes positioned in the device middle region may be on a layer above the other interconnects. Accordingly, the devices can be built in layers 210 by repeating steps 4.b), 4.c), 4.d) and 4.e) in example 3.
  • the pattern of external contact shown in this example is designed to be compatible with Multichannel System amplifiers for Glass MEA (alternative 3), described in 4.f)ii.
  • top insulation four layers are illustrated in the top inset figure, including top insulation.
  • One layer is illustrated as having a thickness of 20 pm.
  • the portions of the insets with the dimensions are illustrative electrode contact dimensions.
  • Multiple layers 230 are schematically illustrated, and reflect that the interconnects and/or electrode contacts may span multiple layers.
  • Example 3 Fabrication Method of the Micro Electrode Array
  • the devices provided herein can be implanted under the pia matter, flush against the brain’s surface.
  • axons and dendrites from grafted neurons reach the opening in the well, they can synapse onto nearby dendrites from the neural tissue.
  • the axons in electrical contact with the tissue can then conduct electric activity stimulated by the electrodes.
  • cells near the device will project axon collateral which synapses with dendrites in the wells, conducting signals to grafted cells.
  • the device itself is dielectric (e.g., the device surface is effectively grounded so that signals cannot leak between cells and unwanted signals cannot leak from tissue to the device), the electric field cannot reach neighboring wells.
  • interference is limited by the number of cells in each well, a number controllable by device dimensions and cell culture parameters, such as plating density.
  • Electrode array suitable for containing cells configured to electrically interface with a biological tissue.
  • One example of a method of making the device includes that summarized in FIGs 2A-2E and as further explained below:
  • An alternative formulation is a mixture of PDMS, Silver, and 2-hydroxy- 2-methylpropiophenone. This mixture is also photosensitive and can be patterned directly. [17] iv. Carbon Black is interchangeable with silver particles [18] for the mixture in part iii. d.
  • Conductive PDMS should be degassed using the same method described in b). reate the array of wells by pouring and casting PDMS. The electrode body can be created upside down. a. an initial grounding layer of conductive PDMS may be spin-coated onto the master. There will likely be a significant accumulation of solution at the rising edges away from the center of the wafer [19] [20], this is not expected to cause an issue because the electrode is much wider than tall.
  • the grounding layer is attached as a final step because a thin layer of conductive PDMS could coat the columns too and it may be desirable to avoid or minimize such a coating location.
  • the grounding layer may be fabricated separately and attached by oxygen plasma bonding after detaching from the master.
  • b. Apply vacuum to remove remaining gas bubbles and allow solution to settle for 30 minutes.
  • c. Bake wafer at 150°C for 2 hours to cure.
  • d. Flow non-conductive PDMS solution into the master and precisely control the level of solution via one of the following methods: i. by precisely measuring the quantity of solution used.
  • This volume can be calculated by weighting the master after step 1 to determine mass removed by bulk surface micromachining. ii. removing excess solution using a glass microscope slide with a round on the leading edge. The slide will move across the top of the master with a weight applied. iii. silanize a glass or silicon wafer with MPTS: (3- mercaptopropyl)triethoxysilane using standard techniques [53], Hold the master (either PDMS or SU8) against the treated wafer under pressure (such as by clamping), flow PDMS mixture between them and cure under pressure. Peel off the wafer after curing the PDMS. e. Repeat step c. to cure. Pattern the electrode contracts in Conductive PDMS a.
  • the minimum thickness of spin-coated thin PDMS layer can be approximately 20 microns, including between 15 pm and 50 pm, and any subranges thereof.
  • Conductive PDMS can be patterned in one of two ways, depending on if a photo- reactive PDMS mixture from step 2.c. is used. Note that if formulation 2ci is used, water vapor may form bubbles inside enclosed spaces, and so may be cured at room temperature. i. If the PDMS mixture is not photoreactive, Conductive PDMS is patterned using a metallic photo-resist [24] following a reactive oxygen surface treatment.
  • the exposed area can be etched by Reactive Ion Etching until top surface of non-conductive PDMS layer. A small amount of over-etching ensure no conductive material remains in the exposed area.
  • a photo-reactive PDMS mixture 2.c.ii . or 2.c.iii. can be exposed to UV and selectively developed like a photoresist.
  • Non-Conductive PDMS can be spin coated on the top surface to create insulation between layers, repeat degassing and curing steps. Holes for interconnects between layers can be patterned onto the insulation or punched afterwards. e. Repeat step b., c., and d.
  • Example 3 is another embodiment related to Example 3, with manufacturing steps that can supplement or replace any of the steps provided in Example 3, as noted herein.
  • FIG. 3 schematically illustrates parts of a manufacturing process showing, for simplicity, a single well and its immediate vicinity, as a flow chart of steps.
  • the process can be used for an array of wells and is compatible with any of a range of known processes in the art related to substrate micrometer-sized handling, deposition, etching, and equivalents thereto.
  • 300 illustrates a SU-8 master comprising a pillar positioned at a corresponding well location.
  • 300 is preferably an array of pillars corresponding to wells of the microarray.
  • the SU-8 master is functionalized, such as by silanization, to facilitate removal of the SU-8 master from another layer of material, such as a PDMS-based layer, including by peeling of the arrays from the SU-8 master.
  • step 310 PDMS is cast over the master 300 to form a PDMS body 312, Preferably, PDMS body 312 is not conductive.
  • step 320 the PDMS body 312 is etched until the top surface 322 of the SU-8 pillars 300 are exposed.
  • Conductive interconnects are subsequently patterned by applying any of a variety of techniques, such as surface machining process, so long as the techniques is compatible with PDMS-based materials.
  • Conductive interconnects are formed from PDMS based conductive composite. The subsequent paragraph provides two specific examples of patterning: by masking and etching or by channel filling.
  • Pattern by masking and etching [21]: prepare positive and negative photomasks of each interconnect layer; optionally perform reactive oxygen treatment of the wafer; transfer negative photomask to aluminum hard mask on the top surface.
  • a protective mask 332 is provided on the PDMS top surface and in step 340 a conductive path layer 342 is provided, such as by spin coating a PDMS based conductive composite.
  • PDMS PDMS, PEDOTPSS, Triton X-100 and ethylene glycol [15]; PDMS and carbon black [32]; PDMS and carbon nanotubes [37] [33] ; PDMS and silver powder or silver nano wires [34],
  • an etch mask 352 is provided to the positive photomask, such as an aluminum hard mask that is resistant to the PDSM etching of subsequent step 360, also generally referred to as an etch down step that removes PDMS-based material that is positioned over mask 332.
  • PDMS etching is by any of a range of techniques known in the art, including: Dry Reactive Ion Etching (DRIE) using, for example CF4 and 02 or SF6 and 02; Wet etch using NMP(N-methyl pyrrolidinone) and TBAF (tetra-butyl ammonium fluoride). [36]; Combined wet/dry process, where dry etch by CF4 and 02 is followed by wet etch. [24]; Wet etch using concentrated sulfuric acid. [38],
  • DRIE Dry Reactive Ion Etching
  • step 380 insulation 382 is applied over conductive path layer 342, such as by an additional layer of PDMS by oxygen plasma treatment [39], [40], In step 390 the arrays are detached and in step 400 bonded to a grounding layer 402.
  • step 410 An alternative to steps 330-380 of FIG. 3 is shown in FIG. 4, with initial steps 310 and 320 the same as in FIG. 3.
  • step 410 a new positive master 412 is provided and in step 470 a PDMS negative 472 of the interconnect layer is cast.
  • the PDMS negative 472 is detached in step 475.
  • step 480 the PDMS negative 472 is bonded to the top surface 473 of the device body, such as by oxygen plasma treatment of both adjacent surfaces.
  • a punch hole 486 is made in step 485 to provide access via injection of a PDMS based conductive composite 491 and subsequent curing as illustrated in step 490. Note that the composite containing ethylene glycol will form bubbles when heated and should not be cured in an oven.
  • steps 390 and 400 are the final steps where the wells and the interconnects are bond to the separately created grounding layer.
  • Conductive grounding layer and/or arrays for bulk interfacing are bond to the tissue-facing side by reactive oxygen treatment (see, e.g., step 400). Wafers are cut into devices and bonded to wires.
  • a particularly important aspect of the instant devices and methods is the ability to reliably add neuronal cells to the electronic device that is in the form of a microarray.
  • Neuronal cells in other words, can effectively be grafted to the device and ready to make an electrical connection with biological tissue.
  • the electrical connection is fundamentally improved herein, in that each individual electrical connection between device (e.g., a neuronal cell in the well) and tissue is to as few as less than 10 cells in the tissue, less than 5 tissue cells, or as few as 1 tissue cell.
  • the tissue cell may be in a tissue such as brain, spinal cord, or a peripheral nerve.
  • IPSC linage are commercially available (for example ATCC’s ACS1019).
  • IPSC is induced to differentiate into neurons or precursors
  • IPSC derived cells are commercially available(see, e.g., Elixirgen Scientific’s QuickNeuronTM Series).
  • compatible neurons are obtained from an inbred rat strain, a bio-engineered twin or a cloned embryo.
  • PDMS is extremely hydrophobic, therefore action must be taken to improve surface adhesion, especially if step 3a is not taken. Cover the PDMS devices with culture media for several hours, to allow protein to absorb onto the surfaces, (a) Optionally, after covering the devices with culture media, transfer the dishes to a low vacuum, until bubbles in the wells dissolve into the media.
  • Collagen e.g. GibcoTM A1048301
  • Resistive and capacitive leaks between wells without grafted cells may be tested without grafted cells. It is possible to test if stimulation artifacts appears in other channels without the cells. This test is especially important for dense arrays.
  • the device surface facing the tissue is a solid conductive grounding layer, and so there should be no current flow between wells. This aspect is relevant for achieving high specificity between device and the tissue.
  • the device can be directly visualized, including with a confocal microscope, by supporting the device with a microscope slide.
  • the device can be fixed in a dish and sectioned, such as sliced with a vibrotome, and stained (for example, with Nissil stain) for imaging, including by a transmission microscope. This aspect is useful for assessing if grafted cells are viable and living (live vs. dead stain).
  • Example 7 CELL TYPE TARGETING
  • Targeting synaptic connections (a) The type of cells grafted to the electrodes of the array influences the counter-part corresponding nearby cell (from the biological tissue) that forms a synaptic contact. This can be leveraged with targeted gene expression, to facilitate connection with only certain types of neurons in the brain, (b) This is a relevant consideration in view of the fact that the brain comprises different types of neurons in different brain regions. [0127] The devices and methods are compatible with a range of cell types, including commercially-available cell types and custom-isolated cell types, so long as they can be provided at a low cell number to each well and are able to reliably secure electrical connection to a biological tissue.
  • IPSC derived cells may be used to target specific type of neurons.
  • Different types of neurons for example Motor, Sensory, Cholinergic, Dopaminergic, GABAergic
  • This can be used to communicate with specific type of cells in the vicinity of the array
  • Examples of commercially available cell types for use with the instant devices and methods include, but are not limited to, those provided in TABLE 1.
  • Example 8 Animal Surgery [0130] 1) Electrode implantation: Chronic Neural recording techniques are well established [52], Procedures are conducted in compliance with sterile, anesthesiology, and animal ethics protocols.
  • In-Vivo behavioral tests are based on delayed nonmatch-to-sample tests, which are described elsewhere [30], The behavioral test can be used to validate and verify the system: (a) Train the animal to select a lever from n (e.g. 5) after hearing a tone. The animal must press a lever after hearing a tone to receive a sugar pellet. Only the first lever pressed is considered. Afterward, all the lever withdraw and can no longer be pressed until the next trial, (b) Initially the selection is based on the sound played, (c) After the animal become familiar with (a) and (b), the lever to be pressed is transmitted as an electrical stimulus pattern over the array.
  • n e.g. 5
  • the behavioral test can be used to validate and verify the system: (a) Train the animal to select a lever from n (e.g. 5) after hearing a tone. The animal must press a lever after hearing a tone to receive a sugar pellet. Only the first lever pressed is considered. Afterward, all the lever withdraw and can no longer
  • a tone not used in b) is played, (d) Animal behavioral performance in (c) and (a) is compared, as well as the chance of randomly guessing the correct lever (e.g. 20%). (e) The neural activity after presentation of the stimulus pattern is recorded by the electrode array and transmitted to a computer for analysis, (f) After termination of the experiment, the brain is fixed for histological analysis to determine the extent of integration between the brain and grafted cells.
  • High specificity The main aspects of the devices and methods of using the devices provided herein, and advantage over conventional existing devices, are those that provide the extremely high specificity between the electric contact and target neurons. This is achieved by providing a brain-facing surface of the device that functionally acts as a ground in combination with the grafted cells in the wells, so that electrical current can only flow as action potentials to or from the grafted cells. The grafted cells, in turn, will only synapse with one or the few cells that they can physically reach. This combination of grounded tissuefacing surface, grafted cells in the wells, and physical connection between the grafted cells and biological cells of the tissue provides the high specificity.
  • Power Efficiency Furthermore, there is about one cell, or at most several cells (e.g., less than 10, less than 5, or less than 3) per contact to the target biological tissue. Such a few number of cells that synaptically connect at a particular location provides a number of functional benefits, including a signal from each cell can be transformed into a spike train with a threshold circuit. This results in a greatly reduced power consumption by a device, including a device that is a head stage. Conventional head stages historically have a serious problem with power consumption, particularly for implantable/integrated head stages. The instant devices and methods have reduced power consumption, particularly as the devices and methods are effectively working with action potentials instead of analog systems with attendant transmission requirements.
  • Noise Resistance because there is only one or a few cells in every well, every channel will pick up spike trains corresponding to these cells, which are in effect carrying only timing information. Noise from local field potentials that penetrates the wells cannot disrupt the operation because they distort the spike trains vertically rather than horizontally. The cellular electrode can tolerate a large amount of noise before breaking down, making it tolerant to internal or external noises.
  • High Bandwidth The first part of the fabrication process is the same for a Utah array. Therefore the instant devices can achieve the same array density as the number of needles in state-of-art Utah array. With a spacing of 100 pm, a 10 X 10 mm array can contain up to 10,000 unique contacts. Because electrical interconnects will be routed through multiple conductive polymer layers, this density is possible. In practice, however, the density may be limited to the channel count of the best amplifier systems.
  • the devices provided herein also have good temporal resolution.
  • the response of grafted neurons serving as electrical connection can be predicted using the pulse waveform, cell type and well geometry.
  • the device is formed from the polymer, including from PDMS.
  • PDMS is an elastic material which can have a mechanical parameter, such as a Young’s modulus, matched to the to-be-interfaced tissue. Therefore, there will be minimal abrasion between the electrode array and the neural tissue due to mismatch in mechanical properties.
  • PDMS is also biologically inert, non-toxic and tends not to trigger immune responses. Accordingly, the device is suitable for long term use with biological tissue, including in vitro, ex vivo and in vivo.
  • the device can also be rolled into a cuff electrode configuration, suitable for electrically interfacing with the spinal cord or peripheral nerves.
  • PDMS is optically clear and so the device can be viewed directly with a transmission microscope.
  • the device is sufficiently soft that it can be cut with a vibrotome and scanned by a confocal microscope. This makes the device an excellent solution for long-term in vitro studies, such as organotypic cultures.
  • the device may be designed to incorporate head stage electronics.
  • the device can also be made compatible with any amplifier that accepts a micro-ribbon connector. This can be done by bonding or directly patterning Parylene ribbons on the device.
  • the device may be made to have only 32 or 64 channels. This allows the device to be tested using existing TBSI or Multichannel system head stage amplifiers.
  • Segmented numerical model (with NEURON) can be created for dendrite and axon from grafted cells (following gradients) and towards grafted cells (against gradients). Simulations are performed to predict spike trains triggered by time-varying potential gradient (for stimulation) or the extracellular potentials generated by moving action potentials (for recording). These models are used to guide design parameters. Cell morphology obtained from confocal microscopes are used to verify the models.
  • the distribution of number of cells in wells is expected to be a Poisson distribution. Therefore, to limit the number of wells with multiple cells, a large number of wells may be empty. This situation can be improved by cell capture and handling techniques provided in various micro-fluid devices.
  • the number of cells per well is controlled via microfluidics.
  • cell sorters see, e.g., fluorescent activated cell sorters FACS
  • a FACS can provide a single cell from a nozzle. The nozzle can be connected to a custom setup on a floating air table, where a micro manipulator moves a petri dish containing the array at a fixed speed. Therefore, a single cell can be placed at each well, as desired.
  • neural signal are conducted mostly passively in dendrite and actively in axons, it is better for stimulation if grafted cells send axons into the adjacent tissue. Conversely it is better for recording if adjacent cells send axons to synapse onto grafted cells.
  • the devices described herein comprise an electrode array for a neural interface which achieves high specificity using grafted cells in concert with special conductive and non-conductive polymer layers and regions. In this manner, the devices and related methods of using the electrode array devices, outperform all systems currently on the market, including for chronic applications.
  • a standard surface electrode array 240 (see, e.g., FIG. IB) is fabricated on the tissue-facing layer with standard techniques, to provide the desired specificity and ability to obtain a bulk aggregate electrical interface with tissue.
  • This secondary electrode array can be positioned on the top-most biological-facing tissue instead of part of the ground. This facilitates simultaneous collection of more “bulk” or “overall” electrical signals.
  • This embodiment is particularly useful for debugging or serving as a backup. Of course, there is an attendant impact with respect to ground being imperfect; the imperfect ground can be accommodated by increasing device thickness.

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Abstract

L'invention concerne des électrodes ayant au moins une cellule neuronale greffée configurée pour se connecter électriquement à un tissu cible par l'intermédiaire de la cellule neuronale greffée. L'invention concerne également des réseaux d'électrodes cellulaires et des méthodes associées aux réseaux d'électrodes et d'électrodes cellulaires. Le réseau a un substrat polymère flexible ayant une surface supérieure et un réseau de puits disposés dans le substrat polymère flexible. Les puits sont configurés pour recevoir une cellule neuronale et fournir une croissance dirigée d'axones et de dendrites bourgeonnants à partir de la cellule neuronale dans une direction vers le haut du puits. De cette manière, le réseau d'électrodes cellulaires peut avoir une spécificité élevée, y compris pour une interface électrique, par l'intermédiaire d'un contact électrique entre les cellules neuronales dans chaque puits et un tissu biologique correspondant et des cellules biologiques spécifiques. La configuration de réseau fournit la capacité d'établir une interface électrique avec un tissu cible généralement aligné sur le réseau de puits.
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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2014045618A1 (fr) * 2012-09-19 2014-03-27 独立行政法人科学技術振興機構 Formation d'un réseau de cellules nerveuses ainsi qu'application associée, et dispositif d'ensemencement de cellules nerveuses
US20190126043A1 (en) * 2016-04-14 2019-05-02 The Trustees Of The University Of Pennsylvania Implantable living electrodes and methods for use thereof
US20220176105A1 (en) * 2019-03-25 2022-06-09 The Board Of Trustees Of The Leland Stanford Junior University Honeycomb-shaped electro-neural interface for retinal prosthesis
WO2022182723A1 (fr) * 2021-02-24 2022-09-01 The Trustees Of The University Of Pennsylvania Tissu neuronal préformé permettant une restauration ou une augmentation d'entrées auditives dans le cerveau
WO2022221682A1 (fr) * 2021-04-15 2022-10-20 University Of Utah Research Foundation Microélectrodes de transition implantables

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2014045618A1 (fr) * 2012-09-19 2014-03-27 独立行政法人科学技術振興機構 Formation d'un réseau de cellules nerveuses ainsi qu'application associée, et dispositif d'ensemencement de cellules nerveuses
US20190126043A1 (en) * 2016-04-14 2019-05-02 The Trustees Of The University Of Pennsylvania Implantable living electrodes and methods for use thereof
US20220176105A1 (en) * 2019-03-25 2022-06-09 The Board Of Trustees Of The Leland Stanford Junior University Honeycomb-shaped electro-neural interface for retinal prosthesis
WO2022182723A1 (fr) * 2021-02-24 2022-09-01 The Trustees Of The University Of Pennsylvania Tissu neuronal préformé permettant une restauration ou une augmentation d'entrées auditives dans le cerveau
WO2022221682A1 (fr) * 2021-04-15 2022-10-20 University Of Utah Research Foundation Microélectrodes de transition implantables

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