US20120065701A1 - Grooved Electrode and Wireless Microtransponder System - Google Patents
Grooved Electrode and Wireless Microtransponder System Download PDFInfo
- Publication number
- US20120065701A1 US20120065701A1 US13/298,185 US201113298185A US2012065701A1 US 20120065701 A1 US20120065701 A1 US 20120065701A1 US 201113298185 A US201113298185 A US 201113298185A US 2012065701 A1 US2012065701 A1 US 2012065701A1
- Authority
- US
- United States
- Prior art keywords
- electrode
- housing
- groove
- grooved
- peripheral nerve
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
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
- A61N1/0551—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
- A61N1/0526—Head electrodes
- A61N1/0529—Electrodes for brain stimulation
- A61N1/0536—Preventing neurodegenerative response or inflammatory reaction
-
- 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
- A61N1/02—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
- A61N1/0556—Cuff electrodes
Definitions
- Embodiments of the invention relate generally to systems and methods for interfacing cellular matter, particularly, to systems and methods facilitating signal communication between devices interfacing cellular matter and external systems.
- disorders and/or diseases of neurological system(s) within the human body may include paralysis due to spinal cord injury, cerebral palsy, polio, sensory loss, sleep apnea, acute pain, and so forth.
- a characterizing feature of the aforementioned disorders and/or diseases may be, for example, the inability of the brain to neurologically communicate with neurological systems dispersed throughout the body. This may be due to physical disconnections within the neurological system of the body, and/or to chemical imbalances, which may alter the ability of the neurological system to receive and/or transmit electrical signals, such as those propagating between neurons.
- Advances in the medical field have produced techniques aimed at restoring or rehabilitating, to some extent, neurological deficiencies leading to some of the above-mentioned conditions. Further, such techniques may typically be aimed at treating the central nervous systems and, therefore, are quite invasive. This may include, for example, implanting devices, such as electrodes, into the brain and physically connecting, via wires, those devices to external systems adapted to send and/or receive signals to or from the implanted devices.
- implanting devices such as electrodes
- wires those devices to external systems adapted to send and/or receive signals to or from the implanted devices.
- the incorporation of foreign matter and/or objects into the human body may present various physiological complications, rendering such techniques very challenging to implement. For example, the size and extension of the implanted devices and wires extending therefrom may substantially restrict patient movement.
- an implanted device typically requires a built-in battery so that it can operate. If the device is to remain within the body for prolonged periods of time, such batteries are frequently replaced, requiring additional surgical procedures that could yet lead to more complications.
- FIG. 1 illustrates a plurality of grooved electrodes implanted inside a human body, in accordance with an embodiment of the present technique
- FIG. 2 is a perspective view of a grooved electrode, in accordance with an embodiment of the present technique
- FIG. 3 is a front cross sectional view of a portion of the grooved electrode shown in FIG. 2 , in accordance with an embodiment of the present technique
- FIG. 4 is an exploded perspective view of a grooved electrode fitted with a neuro-microtransponder, in accordance with an embodiment of the present technique
- FIG. 5 is a schematic circuit diagram of the neuro-microtransponder, in accordance with an embodiment of the present technique
- FIG. 6 is a schematic diagram illustrating the manner of operation of the neuro-microtransponder, in accordance with an embodiment of the of the present technique
- FIG. 7 is a perspective view of another embodiment of grooved electrodes, in accordance with the present technique.
- FIG. 8 is a front view of the grooved electrodes shown in FIG. 7 ;
- FIG. 9 is a perspective view of another configuration showing grooved electrodes, in accordance with an embodiment of the present technique.
- FIG. 10 is a front view of the configuration shown in FIG. 9 , in accordance with an embodiment of the present technique.
- FIG. 11 is block diagram of a method for interfacing cellular matter, in accordance with an embodiment of the present technique.
- a grooved electrode 10 is shown as being implanted inside a human body 12 , in accordance with an embodiment of the present technique.
- the grooved electrode 10 is adapted to be implanted within the body 12 for interfacing cellular matter.
- the grooved electrode 10 can be incorporated within the nervous system of the body 12 , more particularly, within peripheral nerves of the nervous system.
- a peripheral nerve may be comprised of multiple nerve fibers, where each fiber includes one axon.
- the grooved electrode 10 may comprise biocompatible materials and/or components, enabling the grooved electrode 10 to assimilate and become part of the axons of the peripheral nervous system for extended periods of time.
- the grooved electrode 10 may be physically and/or chemically designed for promoting growth of cellular mater, such as axons of peripheral nerves, along portions of the grooved electrode 10 and/or in its vicinity. This enables the grooved electrode 10 to better mesh with the cellular matter, i.e., peripheral nerves, thereby enabling components of the grooved electrode 10 to optimally interact with the cellular matter. Further, by virtue of its adaptability to peripheral nerves, the grooved electrode 10 may be implanted within the body 12 using minimally invasive methods, thereby reducing risks of infections and/or other complications.
- cellular mater such as axons of peripheral nerves
- the grooved electrode 10 may include a wireless neuro-microtransponder ( FIG. 4 ) configured to interact with certain portions of the peripheral nervous system.
- the wireless neuro-microtransponder incorporated within the grooved electrode 10 is adapted to convey signals, such as neurological signals, to or from the human body 12 .
- systems external to the body 12 may employ the grooved electrode 10 as an interface for detecting, transmitting, or otherwise facilitating communication of electrical signals induced by various physiological processes occurring between various anatomical structures or communication of signals for actuating biomechanical devices.
- the grooved electrode 10 can be used with prosthetics for providing a neural interface between portions of the body 12 , which are naturally anatomical, and portions of the body 12 , which may be artificial, such as artificial limbs.
- arm 14 may include a natural, i.e., non-prosthetic, portion 16 coupled to a prosthetic portion 17 adapted to act as an artificial extension of the arm 14 .
- a plurality of the grooved electrodes 10 may be disposed throughout portions 16 of the arm 14 and shoulder area of the body 12 .
- the grooved electrodes 10 can be used to wirelessly open neurological pathways between the brain and/or natural anatomical structures, such as between the portion 16 and the prosthetic 17 .
- the prosthetic 17 may incorporate biomechanical devices 18 adapted to receive signals generated by peripheral nerves within portion 16 of the arm 14 .
- the biomechanical devices 18 may include electromechanical devices some of which may be similar to the grooved electrode 10 .
- the prosthetic 17 can be actuated with sufficient strength, dexterity, and sensitivity, enabling a person to control the prosthetic 17 as if the prosthetic were a natural extension of the human body.
- the grooved electrodes 10 may be used to treat patients suffering from obstructive sleep apnea.
- the grooved electrodes 10 may be implanted within the head of the body 12 , specifically, within nerves controlling muscles of the soft palate around the base of the tongue.
- the grooved electrode 10 may be used to electrically stimulate a hypoglossal nerve so as to prevent the aforementioned muscles from obstructing breathing airways of the patient. Still in other instances, the grooved electrodes 10 may be used to treat patients suffering of persistent and/or acute pain by stimulating the peripheral nerves to cause paresthesia of an area where pain is felt.
- the plurality of grooved electrodes 10 may be employed as a neurological interface enabling neurological signals to propagate throughout anatomical regions of the body 12 whose neurological pathways are compromised or are otherwise absent.
- the grooved electrode 10 may be employed as a neurological interface enabling neurological signals to propagate throughout anatomical regions of the body 12 whose neurological pathways are compromised or are otherwise absent.
- peripheral nerves may include fiber pathways that play an important role in propagating neurological signals, such as those needed to control the prosthetic portion 17 of the arm 14 .
- grooved electrodes 10 may specifically be designed and configured to mechanically and electrically interface with such peripheral nerves.
- each of the grooved electrodes 10 may be smaller than 1 millimeter, and each may be adapted to detect axonal spike signals, whose magnitudes are as low as 10 microvolts.
- the grooved electrode 10 may include, for example, bio-synthetic nerve guides with electrically sensitive carbon nanotubes adaptable to pick up weak electrical spike signals generated by individual peripheral nerve axons.
- the grooved electrode 10 may include neurotrophic factors adapted for promoting growth and fusion of axons within a mesh of carbon nanotubes disposed within a nerve guide leading to components of the grooved electrode.
- each of the grooved electrodes 10 incorporates a wireless neuro-microtransponder enabling each of the grooved electrodes 10 to receive and transmit signals to or from the body 12 .
- a coil 19 may be disposed about portions of body 12 , particularly, about those portions in which the grooved electrodes are implanted for facilitating wireless communication between the grooved electrode 10 and external systems.
- the coil 19 is adapted to generate electromagnetic signals, such as radio frequency (RF) signals, which can be intercepted by various circuit components of the transponder. As discussed further below, such circuit components are adapted to modulate the received RF signals in response to electrical signals generated by the peripheral nerves detected by the grooved electrode 10 .
- RF radio frequency
- the grooved electrodes 10 may sense neurological signals, such as those propagating from the brain via the arm 14 , aimed at moving the prosthetic 17 . Accordingly, the transponder senses such signals and, in so doing, modulates the RF signals generated by the coil 19 .
- the coil 19 receives the modulated RF signals, which could then be analyzed to determine the nature of the desired movement. Thereafter, the coil 19 may generate RF signals for actuating the biomechanical devices 18 , thereby enabling the prosthetic 17 to move according to the desired movements.
- the RF signals generated by the coil 19 are further adapted to power the transponder of the grooved electrode 10 , thereby eliminating the incorporation of power supplies, i.e., batteries, within the grooved electrode 10 .
- This may simplify electrical transponder circuitry, which could promote the miniaturization of the grooved electrode 10 and components thereof. This may further enable clinicians to implant the grooved electrode 10 within the body 12 with relative ease and accuracy.
- the ability to RF power the grooved electrode 10 may prevent patients from undergoing repetitive invasive surgical procedures needed for replacing batteries, such as those used in existing systems.
- each of the grooved electrodes 10 may form a single autonomous wireless unit adapted to independently interact with peripheral nerves, as well as with other grooved electrodes and/or other systems disposed in its vicinity.
- the wireless feature of the grooved electrodes 10 may replace wire-coupled systems, thereby unrestricting patient movement.
- FIG. 2 is a perspective view of the grooved electrode 10 , in accordance with an embodiment of the present technique.
- the grooved electrode 10 includes a hollow elongated rectangular body 20 forming an encasement through which electronic components can be inserted and housed.
- the body 20 has grooves 22 extending lengthwise throughout the body 20 .
- the grooves 22 are adapted to facilitate growth of cellular matter, i.e., peripheral nerves, about the exterior portions of the grooved electrode 10 .
- the grooved electrode 10 may be shaped to have certain geometrical features and characteristics corresponding to those portions of anatomies in which the grooved electrode 10 is implanted.
- the grooved electrode 10 may be shaped to have a length of less than two millimeters with the width and the height being much smaller than its length. Such dimensional characteristics of the grooved electrode 10 may correspond to the length of an active current zone generated during a peak spike phase of an active nerve fiber, as may be appreciated to those skilled in the art. In accordance with the present technique, this enables the grooved electrode 10 to have sufficient contact with peripheral nerve fibers growing along the grooved electrode 10 , thereby providing robust signal-sampling capabilities during the peak spike phase of the nerves. It should be appreciated that the grooved electrode 10 may attain shapes and sizes other than the one illustrated by FIG. 1 , such as those for accommodating implantation of the groove electrode through various portions of the body 12 ( FIG. 1 ).
- the body 20 of the grooved electrode 10 may be formed of a biocompatible polymer adapted to seal and insulate components and/or devices, i.e., transponder ( FIG. 4 ), encased within the body 20 .
- a biocompatible polymer may include FDA-approved polymer materials, such as polymethylmethacrylate (PMMA), polydimethylsiloxane (PDMS), polytetraflouroethylene (PTFE), parylene, as well as biocompatible forms of polyurethane or polycarbonate.
- PMMA polymethylmethacrylate
- PDMS polydimethylsiloxane
- PTFE polytetraflouroethylene
- parylene parylene
- the grooved electrode 10 includes an opening 24 disposed at one of the body 20 through which the microtransponder ( FIG. 4 ) is fitted.
- the microtransponder FIG. 4
- peripheral nerve fibers grow lengthwise along the grooves 22 , a configuration is achieved whereby the peripheral nerves encase the transponder disposed within the body 20 .
- electrode leads 26 disposed along the grooves 22 are adapted to electrically connect axons of the peripheral nerves growing along the grooves 22 with the transponder encased within the body 20 .
- the transponder may form an interface capable of sensing or stimulating those axons disposed directly in the vicinity of the groove electrode 10 .
- the grooved electrode 10 may be coupled to wire leads 30 , configured to electrically couple the grooved electrode 10 to external devices, such as other grooved electrodes.
- the wire leads 30 may be adapted for delivering power to components disposed within the grooved electrode.
- the wire leads 30 are also adapted to transfer electrical signals, such as those generated by neurons, or those used for stimulating the neurons of a peripheral nerve.
- the aforementioned functionalities could also be achieved by using wireless techniques, as explained further below.
- the grooves 22 may be carved throughout four edges of the grooved electrode 10 .
- FIG. 3 which is a front cross-section of FIG. 2 taken along line 3 - 3
- each of the grooves 22 and the body 20 houses the electrode lead 26 , which extends lengthwise along the grooves 22 .
- the electrode lead 26 may be embedded within the body 20 such that a portion of the electrode lead 26 may be fully engulfed by the body 20 , while a remaining portion of the electrode lead 26 may be exposed to an opening formed by the groove 22 .
- electrode leads 26 are adapted to contact those axons 28 growing along the opening of the grooves 22 , thereby forming an electrical connection between the axons and contact leads of a neural micro-transponder disposed within the grooved electrode 10 .
- This electrical connection permits electrical current to flow between the neural axons 28 and the transponder as, for example, may occur during detection of spike signals.
- electrode leads 26 may be made from conductive carbon nanotube or other nano-scale structures having neurotrophic properties.
- electrode leads 26 may be made from electrically conductive, biocompatible, and corrosion-resistant materials including metallic alloys, such as medical-grade stainless steel, gold, platinum, and/or a combination thereof.
- Other suitable materials from which the electrode leads 26 may be formed include inert-non-metallic conductors, such as graphite or polymer composites.
- the grooves 22 are carved along the body 20 in a manner permitting proper growth of the axons 28 lengthwise within the groove along the exterior portions of the grooved electrode 10 .
- the grooves 22 may be shaped to have certain dimensional characteristics.
- the grooves 22 may be carved so as to permit healthy maturation of at least one nerve fiber.
- the grooves 22 may be carved to be small enough for minimizing the number of fibers exposed to the electrode lead 26 .
- the aforementioned attributes may be achieved by fabricating the grooves 22 to be approximately 10 micrometers in depth and width.
- the opening defined by each of the grooves 22 may be shaped to have a unique profile.
- the opening of the groove 22 may be profiled to have a U, V, or rectangular shape.
- the illustrated V-shaped profile may render the opening of each of the grooves 22 to be approximately 15 micrometers wide, tapering down to approximately 5 micrometers at the exposed electrode surface at the floor or fundus of the groove. It should be born in mind that the openings of the grooves 22 may be shaped to accommodate varying needs, as prescribed by physiological, anatomical, and/or clinical constraints.
- the grooved electrode 10 may be configured to optimally contact and stimulate individual nerve fibers that grow along the grooves 22 .
- the above-mentioned design of the grooves 22 is adapted to permit unrestrained fiber growth, thereby eliminating risks of long-term fiber damage, such as those that are associated with existing ‘sieve’ designs.
- the grooves 22 are adapted to isolate fewer fibers that make contact with each electrode lead 26 , thereby providing finer stimulus resolution and more discrete detection of fiber activity.
- the groove may be filled with neurotrophic factors or other biochemicals that guide or otherwise facilitate fiber growth in direct contact with the conductive electrode lead 26 along recessed portions forming the floor of the groove.
- FIG. 4 is an exploded perspective view of the grooved electrode 10 fitted with a wireless neuro-microtransponder 40 , in accordance with an embodiment of the present technique.
- the transponder 40 is adapted to fit within the grooved electrode 10 through the opening 24 .
- the transponder 40 may be inserted within the grooved electrode 10 together with slow releasing neurotrophic substances and anti-inflammatory gels for minimizing aversive tissue reactions and for promoting the proper implantation of the grooved electrode 10 within the body.
- the grooved electrode 10 and the transponder 40 make up a module adapted to physically, electrically, and chemically interact with peripheral nerves located in the vicinity of the grooved electrode 10 .
- axons of peripheral nerves growing along exterior portions of the grooved electrode 10 may electrically interface with the transponder 40 via the electrode lead 26 .
- This configuration enables signals to propagate between the transponder 40 and peripheral nerves.
- the transponder 40 includes wireless components adapted to communicate with systems external to the body, thereby enabling such systems to transmit and receive signals to or from the peripheral nerves within the body in which the grooved electrode 10 is implanted.
- the transponder 40 includes a magnetic core 42 about which microcoils 44 are coiled.
- the microcoils 44 form an inductor adapted to magnetically interact with electromagnetic fields, such as those propagating from sources external to the grooved electrode 10 .
- the microcoils 44 enable the transponder 40 to receive and/or transmit signals from or to the external systems with which the transponder 40 communicates.
- the microcoils 44 are adapted to power the transponder 40 through power induction.
- the microcoils 44 are adapted to received RF signals and convert those into electrical signals used to electrically power components of the transponder 40 . In this manner, the transponder 40 may operate while being battery-free for extended periods of time.
- the core 42 may be fabricated out of nano-crystalline magnetic alloys, adapted for achieving a high inductance (L) at radio frequencies.
- the coils 44 may have an (L) value four orders of magnitude greater than (L) values achieved by inductors formed of conventional materials.
- each coil of the coils 44 may be fabricated to have a diameter that is as small as 100 micrometers, thereby producing an inductance of approximately 10 nano-Henry.
- the core 42 may be fabricated using laser machining methods of nano-crystalline materials, such as cobalt. Fabrication of the coils 44 may also involve employing techniques used in production of micro-electromechanical systems (MEMS) and nano-electromechanical systems (NEMS).
- MEMS micro-electromechanical systems
- NEMS nano-electromechanical systems
- the transponder 40 further includes a portion 46 adapted to encapsulate circuitry of the microtransponder.
- the portion 46 also includes contact leads, which connect between the circuitry and the grooved electrodes 10 .
- the circuitry encapsulated by the portion 46 includes electrical components adapted to sense and/or stimulate the peripheral nerves interfacing with the grooved electrode 10 .
- the portion 46 includes identification (ID) circuitry adapted to generate unique RF signals in response to the neural spike signals generated by the peripheral nerves.
- ID Radio Frequency Identification
- This Radio Frequency Identification (RFID) capability of the transponder 40 is configured to relay neurological activity occurring within the body to systems external to the body. The ID information may also be used to distinguish between a plurality of transponders emitting RF signals simultaneously from their respective grooved electrodes implanted within the body 12 , as shown in FIG. 1 .
- the portion 46 may be coated with conductive materials, such as gold or other biocompatible conductors, to form the electrical connection between the circuitry encapsulated by the portion 46 and the electrode leads 26 disposed within the grooves 22 of the grooved electrode 10 .
- the transponder 40 further includes a capacitor 48 disposed at the rear portion of the transponder 40 .
- the capacitor 48 may be made from a plurality of nano-tube super capacitors, adapted to increase the capacitance (C) of the transponder 40 .
- the capacitor 48 and the coils 44 form an inductor-capacitor (LC) circuit adapted to modulate received RF signals for producing the RFID signal of the transponder 40 .
- LC inductor-capacitor
- FIG. 5 is a schematic diagram of a circuit 60 disposed within the neuro-microtransponder 40 , in accordance with an embodiment of the present technique.
- the circuit 60 includes electrical components adapted to electrically interface with neurons of peripheral nerves, such as those disposed along the grooves 22 of the grooved electrode 10 , discussed hereinabove with relation to FIGS. 2-3 .
- the circuit 60 further includes electrical components, which enable the transponder 40 to wirelessly interact with systems external to the transponder 40 . Such systems may include other transponders implanted within the body or external coils and/or a receiver, such as those shown in FIGS. 1 and 6 , respectively.
- the wireless capabilities of the circuit 60 enable the delivery of electrical signals to or from the peripheral nerves. These include electrical signals indicative of neural spike signals and/or signals configured to stimulate the peripheral nerves.
- the circuit 60 includes the coils 44 coiled about a central axis 62 .
- the coil 44 is coupled in parallel to a capacitor 61 and to a stimulus trigger demodulator 63 , which in turn is coupled to an RF identity modulator 67 via a switch 65 .
- the RF identity modulator 67 is coupled to a rectifier 64 , which in turn is coupled to a spike sensor 66 and to a stimulus drive 70 .
- the rectifier 64 and the spike sensor 66 are both coupled in parallel to a capacitor 48 .
- the spike sensor 66 is coupled to contact lead 68 , thereby electrically connecting the spike sensor 66 to the axon 28 .
- the spike sensor 66 is made up of one or more field effect transistors (FET). As will be appreciated by those of ordinary skilled in the art, the FET may include metal oxide semiconductors field effect transistors (MOSFETS), such as those fabricated using standard small scale or very large scale integration (VLSI) methods. Further, the spike sensor 66 is coupled to the RF identity modulator 67 , which is adapted to modulate an in coming/carrier RF signal in response to neural spike signals detected by the spike sensor 66 .
- the contact leads 68 and 71 to which the sensor 66 and the stimulus driver 70 are connected, respectively, may be part of the portion 46 ( FIG. 4 ), adapted to interface with the axon 28 of the peripheral nerve disposed along the grooved electrode 10 ( FIG. 2 ).
- the neuro-microtransponder 40 to operate as an autonomous wireless unit, capable of detecting spike signals generated by peripheral nerves, and relaying such signals to external receivers for further processing. It should be born in mind that the transponder 40 performs such operations while being powered by the external RF signals. The above-mentioned capabilities are facilitated by the fact that magnetic fields are not readily attenuated by human tissue. This enables the RF signals to sufficiently penetrate the human body so that signals can be received and/or transmitted by the transponder 40 . In other words, the coils 44 are adapted to magnetically interact with the RF field whose magnetic flux fluctuates within the space encompassed by the coils 44 .
- the coils 44 convert the fluctuations of the magnetic flux of the external RF field into alternating electrical current, flowing within the coils 44 and the circuit 60 .
- the alternating current is routed, for example, via the coils 44 into the rectifier 64 , adapted to convert the alternating current into direct current.
- the direct current may then be used to charge the capacitor 48 , thereby creating a potential difference across the FET of the sensor trigger.
- a gate of the FET 66 may be coupled via a contact lead 68 to the axon 28 .
- the gate of the FET may be chosen to have a threshold voltage that is within a voltage range of those signals produced by the neural axons. In this manner, during spike phases of the neural axons, the gate of the FET 66 becomes open, thereby closing the circuit 60 . Once the circuit 60 closes, the external RF field, the inductor 44 , and the capacitor 48 induce an LC response, which modulates the external RF field with a unique modulating frequency.
- the LC characteristic of the circuit 60 can be chosen to determine the unique modulation, thereby providing a desired ID signal for the transponder 40 .
- the FET 66 provides the RF identity modulator 67 with a trigger signal for generating desired RF signal.
- the ID signal may indicate the nature of the neural activity in the vicinity of the transponder 40 , as well as the location of the neural activity within the body. It should be appreciated that the RF capabilities, as discussed above with respect to the circuit 60 , render the neuro-microtransponder a passive device that reacts to incoming carrier RF signals.
- the circuit 60 does not actively emit any signals, but rather reflects and/or scatters the electromagnetic signals of the carrier RF wave to provide signals having specific modulation. In so doing, the circuit 60 draws power from the carrier RF wave for powering the electrical components forming the circuit 60 .
- FIG. 5 may be used to receive signals from the transponder 40 ( FIG. 4 ) in response, to spike signals generated by peripheral nerves
- other components of the circuit 60 of the transponder 40 may include components for stimulating the peripheral nerves using the external RF signals.
- the RF signals received by the coils 44 may be converted to electrical signals, via the stimulus trigger modulator 63 , so as for providing sufficient current and voltage for stimulating the peripheral nerves.
- the stimulus trigger demodulator 63 derives power from an RF carrier signal for powering the stimulus driver 70 , which delivers electrical signals suitable for stimulating the axons 28 . This may be used to treat nerves that are damaged or that are otherwise physiologically deficient.
- FIG. 6 is a schematic diagram of a system 80 used for interfacing cellular matter, in accordance with an embodiment of the present technique.
- the system 80 is adapted to wirelessly interface with cellular matter, such as peripheral nerves.
- the system 80 is further adapted to receive signals, such as neural spike signals, generated by the peripheral nerves, and analyze those signals to provide feedback and/or treatment to other biological and/or biomechanical systems to which the system 80 is additionally coupled.
- the system 80 includes the neuro-microtransponder 40 interfacing with cellular matter, such as the axon 28 of a peripheral nerve, in a manner described and illustrated hereinabove and shown in FIGS. 1-5 .
- While the present exemplary embodiments may show the single transponder 40 coupled to the axon 28 , other embodiments may include the transponder 40 coupled to more than a single neuron and/or a plurality transponders coupled to a plurality of neurons, some of which may or may not be in close proximity to one another.
- the system 80 further includes the coil 19 disposed in the vicinity of the transponder 40 and the neuron 28 .
- the coil 19 is coupled to an RF signal generator and receiver (RFGRC) 82 , which is coupled to a spectrum analyzer 84 .
- the spectrum analyzer 84 is coupled to a processor 86 , which is also coupled to the RFGRC 82 .
- the RFGRC 82 provides an external RF signal, such as 100 MHz, for powering the transponder 40 and for enabling the transponder 40 to modulate the external RF signal so as to produce an ID signal.
- the modulation frequency produced by the transponder 40 may be two orders of magnitude less than the original RF signal; however, this may vary depending on the type of cellular matter interfaced and the type of transponders used. In embodiments where a plurality of transponders may be employed, a modulation frequency of approximately 1 MHz provides a relatively high bandwidth for the ID signal. This enables the system 80 to distinguish between relatively large amounts of neural-microtransponders responding to electrical neural signals, some of which may be closely coincident.
- the RFGRC 82 receives the modulated RF signal and forwards the signal to the spectrum analyzer 84 for analysis.
- the spectrum analyzer is adapted to determine the modulation frequency, which is then provided to the processor 86 adapted to determine the ID signal characteristic of the spike signal detected by the transponder 40 .
- the processor 86 may prompt the RFGRC 82 to generate RE signals adapted to stimulate other biological and/or biomechanical systems to which additional transponders may be coupled.
- the modulated RF signal received by the RFGRC 82 may originate from neural spike signals generated by peripheral nerves that are severed or are otherwise damaged.
- the processor 86 may prompt the RFGRC 82 to actuate biomechanical devices, such as those incorporated into prosthetics, thereby inducing movement.
- biomechanical devices such as those incorporated into prosthetics
- the capabilities provided by the system 80 for interfacing cellular matter also facilitate treatment of various neurological conditions some of which may include acute pain and obstructive sleep apnea.
- the configuration provided by the system 80 may be adapted to generate load modulation in the transponder 40 by switching the drain-source resistance of the FET of the circuit 60 . This configures the circuit 60 to detect the carrier signal.
- the system 80 may be used for stimulating the peripheral nerves.
- the carrier wave emitted by the external coil 19 may provide the transponder 40 with power for triggering electrodes adapted to deliver electrical signals to the peripheral nerves. In this mode of operation, the powering of the transponder 40 and, thereafter, the stimulation of the peripheral nerves may occur in a periodic sequence in accordance with a specific frequency.
- FIGS. 7 and 8 are perspective and front views, respectively, of another exemplary embodiment of grooved electrodes, in accordance with the present technique.
- grooved electrode 100 may be made up from a substrate 102 conformed to a hollow cylinder populated with grooves 104 extending lengthwise along the interior portion of the cylinder.
- grooved electrode 100 includes electrode leads 106 having a diameter less than 50 micrometers, disposed within the grooves 104 . Similar to the electrode leads 26 discussed above, the electrodes 106 are adapted to contact axons growing along the grooves 22 , thereby forming an electrical connection between the axons and neural micro-transponders, which may be exterior to the grooved electrode 100 .
- the electrode leads 106 may be made from conductive carbon nanotubes, having neurotrophic properties, or from electrically conductive, biocompatible, and corrosion-resistant materials including metallic alloys. Such alloys may include medical-grade stainless steel, gold, platinum, and/or a combination thereof. Other suitable materials from which the electrode 106 may be formed include inert-non-metallic conductors such as graphite or polymer composites.
- the grooved electrode 100 can be constructed by initially embedding a layer of the electrodes 106 within a pre-folded flat substrate 102 formed by casting a biocompatible polymer, such as sylgard. Thereafter, the grooves 104 are carved through the substrate 102 , thereby exposing a portion of each the electrode leads 106 , as illustrated in FIG. 8 . Thereafter, the substrate 102 is rolled into a cylindrical structure forming the grooved electrode 100 . This configuration enables neural fibers to grow and fuse with the interior portions of the grooved electrode 100 .
- the grooves 104 may be filled with biochemical factors promoting fiber growth along the grooved electrode 100 , as well as adhesion thereto.
- the cylindrical structure provided by the grooved electrode 100 can further facilitate formation of artificial fascicles which otherwise form internal structures of peripheral nerves, as appreciated to those skilled in the art.
- FIGS. 9 and 10 are perspective and front views, respectively, of another exemplary embodiment of grooved electrodes, in accordance with the present technique.
- grooved electrode 150 is similar to the grooved electrode 100 discussed hereinabove in that both grooved electrodes 100 , 150 may be formed using similar materials and techniques.
- the grooved electrode 150 is fabricated to form a flattened structure that avoids structural failures which otherwise may result from rolling or flexing the substrate 102 .
- the flattened structure of the grooved electrode 150 may be used to force the fibers in fascicles to grow in contact with the electrode 106 . This may be done, for example, by flattening the grooved electrode 150 to a thickness less than the fascicles, e.g., ⁇ 0.3 millimeter.
- other embodiments may include grooved electrodes having various shapes and configurations adapted to promote growth of cellular matter along the body of the grooved electrodes.
- the electrodes 106 can be disposed along exterior portions of the grooved electrodes.
- Such exemplary embodiments may correspond to, for example, folding the substrate 102 so that the grooves 104 face outward.
- the grooves can promote growth of peripheral nerves along the outer portions of the grooved electrode.
- this configuration may be implemented to produce grooved electrodes having other geometrical shapes, such as of the grooved electrodes shown in FIGS. 9 and 10 .
- FIG. 11 is a block diagram of a method 200 for interfacing cellular matter, in accordance with an embodiment of the present technique.
- the method 200 may be used to wirelessly interface peripheral nerves using devices, such as the grooved electrode 10 , transponder 40 , and system 80 discussed hereinabove and shown in FIGS. 2-4 and 6 .
- the method begins at step 202 in which an RF signal is generated exterior to the cellular matter.
- the RF signal is received by a transponder implanted within the cellular matter.
- the RF signal is adapted to power the transponder so that it can electrically interface with the cellular matter.
- electrical signals generated by the cellular matter are detected by the powered transponder.
- the electrical signals generated by the cellular matter may originate from neural spike signals of peripheral neurons interfacing with the transponder. As discussed above, the ability to detect such spike signals is facilitated by powering the transponder via the RF signal. Thereafter, the method proceeds to step 208 , whereby the RF signal is modulated in response to the detection of the electrical signal produced by the peripheral nerves.
- the modulation of the RF may be unique insofar as it may identify the nature of the signal generated by the cellular matter and/or indicate its origin.
- the modulated RF signal is received and, thereafter, at step 212 the signal is analyzed to determine its ID characteristics. Thereafter, the modulated signal is processed to determine whether to generate additional RF signals to provide additional detection or stimulation of the peripheral nerves, whereby the method 200 returns to step 202 .
Landscapes
- Health & Medical Sciences (AREA)
- Neurology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Neurosurgery (AREA)
- Veterinary Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Psychology (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Electrotherapy Devices (AREA)
- Prostheses (AREA)
Abstract
A grooved electrode adapted for interfacing cellular matter is provided. The grooved electrode includes grooves adapted for electrically interfacing the grooved electrode with cellular matter growing along the body of the grooved electrode. Further, the grooved electrode includes a wireless transponder adapted to electrically interface with cellular matter and to relay such interactions via RF signals. The RF signals received by the wireless transponder are modulated in response to electrical signals generated by the cellular matter, which are detected by the transponder. The grooved electrode may be implanted within peripheral nerves for treating various neurological conditions, which may include nerve rehabilitation and prosthetic actuation, severe pain, obstructive sleep apnea and so forth.
Description
- This application is a continuation of U.S. patent application Ser. No. 12/624,383 field Nov. 23, 2009, which is a divisional of U.S. patent application Ser. No. 11/821,678 filed Jun. 25, 2007 (now U.S. Pat. No. 7,630,771), all of which are hereby incorporated by reference in its entirety.
- Embodiments of the invention relate generally to systems and methods for interfacing cellular matter, particularly, to systems and methods facilitating signal communication between devices interfacing cellular matter and external systems.
- A variety of medical conditions from which people may suffer involve disorders and/or diseases of neurological system(s) within the human body. Such disorders may include paralysis due to spinal cord injury, cerebral palsy, polio, sensory loss, sleep apnea, acute pain, and so forth. A characterizing feature of the aforementioned disorders and/or diseases may be, for example, the inability of the brain to neurologically communicate with neurological systems dispersed throughout the body. This may be due to physical disconnections within the neurological system of the body, and/or to chemical imbalances, which may alter the ability of the neurological system to receive and/or transmit electrical signals, such as those propagating between neurons.
- Advances in the medical field have produced techniques aimed at restoring or rehabilitating, to some extent, neurological deficiencies leading to some of the above-mentioned conditions. Further, such techniques may typically be aimed at treating the central nervous systems and, therefore, are quite invasive. This may include, for example, implanting devices, such as electrodes, into the brain and physically connecting, via wires, those devices to external systems adapted to send and/or receive signals to or from the implanted devices. In addition, the incorporation of foreign matter and/or objects into the human body may present various physiological complications, rendering such techniques very challenging to implement. For example, the size and extension of the implanted devices and wires extending therefrom may substantially restrict patient movement. Moreover, inevitable patient movement may cause the implanted device to dislodge within that portion of anatomy in which the device is implanted. This may result in patient discomfort and may lead to the inoperability of the implanted device, thus, depriving the patient from treatment. Consequently, this may require corrective invasive surgical procedures for repositioning the device within the body, thereby increasing risks of infection and/or other complications. In addition, an implanted device typically requires a built-in battery so that it can operate. If the device is to remain within the body for prolonged periods of time, such batteries are frequently replaced, requiring additional surgical procedures that could yet lead to more complications.
- Hence, there is a need for implantable devices used with systems and/or methods adapted to address the aforementioned shortcomings.
- These and other features, aspects, and advantages of the present invention will become better understood when the following detailed description is read with reference to the accompanying drawings in which like characters represent like parts throughout the drawings, wherein:
-
FIG. 1 illustrates a plurality of grooved electrodes implanted inside a human body, in accordance with an embodiment of the present technique; -
FIG. 2 is a perspective view of a grooved electrode, in accordance with an embodiment of the present technique; -
FIG. 3 is a front cross sectional view of a portion of the grooved electrode shown inFIG. 2 , in accordance with an embodiment of the present technique; -
FIG. 4 is an exploded perspective view of a grooved electrode fitted with a neuro-microtransponder, in accordance with an embodiment of the present technique; -
FIG. 5 is a schematic circuit diagram of the neuro-microtransponder, in accordance with an embodiment of the present technique; -
FIG. 6 is a schematic diagram illustrating the manner of operation of the neuro-microtransponder, in accordance with an embodiment of the of the present technique; -
FIG. 7 is a perspective view of another embodiment of grooved electrodes, in accordance with the present technique; -
FIG. 8 is a front view of the grooved electrodes shown inFIG. 7 ; -
FIG. 9 is a perspective view of another configuration showing grooved electrodes, in accordance with an embodiment of the present technique; -
FIG. 10 is a front view of the configuration shown inFIG. 9 , in accordance with an embodiment of the present technique; and -
FIG. 11 is block diagram of a method for interfacing cellular matter, in accordance with an embodiment of the present technique. - Referring to
FIG. 1 , agrooved electrode 10 is shown as being implanted inside ahuman body 12, in accordance with an embodiment of the present technique. As will be described further below, thegrooved electrode 10 is adapted to be implanted within thebody 12 for interfacing cellular matter. In an exemplary embodiment, thegrooved electrode 10 can be incorporated within the nervous system of thebody 12, more particularly, within peripheral nerves of the nervous system. A peripheral nerve may be comprised of multiple nerve fibers, where each fiber includes one axon. Accordingly, thegrooved electrode 10 may comprise biocompatible materials and/or components, enabling thegrooved electrode 10 to assimilate and become part of the axons of the peripheral nervous system for extended periods of time. In addition, thegrooved electrode 10 may be physically and/or chemically designed for promoting growth of cellular mater, such as axons of peripheral nerves, along portions of thegrooved electrode 10 and/or in its vicinity. This enables thegrooved electrode 10 to better mesh with the cellular matter, i.e., peripheral nerves, thereby enabling components of thegrooved electrode 10 to optimally interact with the cellular matter. Further, by virtue of its adaptability to peripheral nerves, thegrooved electrode 10 may be implanted within thebody 12 using minimally invasive methods, thereby reducing risks of infections and/or other complications. - The
grooved electrode 10 may include a wireless neuro-microtransponder (FIG. 4 ) configured to interact with certain portions of the peripheral nervous system. As will be discussed below, the wireless neuro-microtransponder incorporated within thegrooved electrode 10 is adapted to convey signals, such as neurological signals, to or from thehuman body 12. In so doing, systems external to thebody 12 may employ thegrooved electrode 10 as an interface for detecting, transmitting, or otherwise facilitating communication of electrical signals induced by various physiological processes occurring between various anatomical structures or communication of signals for actuating biomechanical devices. - For example, the
grooved electrode 10 can be used with prosthetics for providing a neural interface between portions of thebody 12, which are naturally anatomical, and portions of thebody 12, which may be artificial, such as artificial limbs. InFIG. 1 ,arm 14 may include a natural, i.e., non-prosthetic,portion 16 coupled to aprosthetic portion 17 adapted to act as an artificial extension of thearm 14. As further illustrated, a plurality of thegrooved electrodes 10 may be disposed throughoutportions 16 of thearm 14 and shoulder area of thebody 12. As discussed further below, thegrooved electrodes 10 can be used to wirelessly open neurological pathways between the brain and/or natural anatomical structures, such as between theportion 16 and theprosthetic 17. Theprosthetic 17 may incorporatebiomechanical devices 18 adapted to receive signals generated by peripheral nerves withinportion 16 of thearm 14. Thebiomechanical devices 18 may include electromechanical devices some of which may be similar to thegrooved electrode 10. - In this manner, the
prosthetic 17 can be actuated with sufficient strength, dexterity, and sensitivity, enabling a person to control theprosthetic 17 as if the prosthetic were a natural extension of the human body. It should be born in mind that while the illustrated embodiment may show thegrooved electrodes 10 as being disposed within thearm 14 for accommodating prosthetic movements, other embodiments may incorporate thegrooved electrodes 10 in other portions of thebody 12 for other purposes. For example, thegrooved electrode 10 may be used to treat patients suffering from obstructive sleep apnea. In such instances, thegrooved electrodes 10 may be implanted within the head of thebody 12, specifically, within nerves controlling muscles of the soft palate around the base of the tongue. For example, thegrooved electrode 10 may be used to electrically stimulate a hypoglossal nerve so as to prevent the aforementioned muscles from obstructing breathing airways of the patient. Still in other instances, thegrooved electrodes 10 may be used to treat patients suffering of persistent and/or acute pain by stimulating the peripheral nerves to cause paresthesia of an area where pain is felt. - As mentioned, the plurality of
grooved electrodes 10, such as those disposed within theportion 16 of thearm 14, may be employed as a neurological interface enabling neurological signals to propagate throughout anatomical regions of thebody 12 whose neurological pathways are compromised or are otherwise absent. To optimize thegrooved electrode 10 for use within the nervous system of thebody 12, those skilled in the art will appreciate the importance in choosing proper tissue sites within which to incorporate thegrooved electrode 10. For example, peripheral nerves may include fiber pathways that play an important role in propagating neurological signals, such as those needed to control theprosthetic portion 17 of thearm 14. To accommodate such attributes,grooved electrodes 10 may specifically be designed and configured to mechanically and electrically interface with such peripheral nerves. For example, each of thegrooved electrodes 10 may be smaller than 1 millimeter, and each may be adapted to detect axonal spike signals, whose magnitudes are as low as 10 microvolts. To detect such minute signals, thegrooved electrode 10 may include, for example, bio-synthetic nerve guides with electrically sensitive carbon nanotubes adaptable to pick up weak electrical spike signals generated by individual peripheral nerve axons. Further, thegrooved electrode 10 may include neurotrophic factors adapted for promoting growth and fusion of axons within a mesh of carbon nanotubes disposed within a nerve guide leading to components of the grooved electrode. - To establish wireless neurological pathways, each of the
grooved electrodes 10 incorporates a wireless neuro-microtransponder enabling each of thegrooved electrodes 10 to receive and transmit signals to or from thebody 12. In the illustrated embodiment, acoil 19 may be disposed about portions ofbody 12, particularly, about those portions in which the grooved electrodes are implanted for facilitating wireless communication between thegrooved electrode 10 and external systems. Thecoil 19 is adapted to generate electromagnetic signals, such as radio frequency (RF) signals, which can be intercepted by various circuit components of the transponder. As discussed further below, such circuit components are adapted to modulate the received RF signals in response to electrical signals generated by the peripheral nerves detected by the groovedelectrode 10. In other words, electrical interactions of the transponder with the peripheral nerves manifest as unique modulations in the RF signals generated by thecoil 19. These modulations are detected by thecoil 19 and, thereafter, undergo further signal processing for identifying the extent and location of the neurological activity within those portions of thebody 12 where thegrooved electrodes 10 are implanted. In an exemplary embodiment, thegrooved electrodes 10 may sense neurological signals, such as those propagating from the brain via thearm 14, aimed at moving the prosthetic 17. Accordingly, the transponder senses such signals and, in so doing, modulates the RF signals generated by thecoil 19. Thecoil 19 receives the modulated RF signals, which could then be analyzed to determine the nature of the desired movement. Thereafter, thecoil 19 may generate RF signals for actuating thebiomechanical devices 18, thereby enabling the prosthetic 17 to move according to the desired movements. - Further, the RF signals generated by the
coil 19 are further adapted to power the transponder of the groovedelectrode 10, thereby eliminating the incorporation of power supplies, i.e., batteries, within the groovedelectrode 10. This may simplify electrical transponder circuitry, which could promote the miniaturization of the groovedelectrode 10 and components thereof. This may further enable clinicians to implant the groovedelectrode 10 within thebody 12 with relative ease and accuracy. In addition, the ability to RF power the groovedelectrode 10 may prevent patients from undergoing repetitive invasive surgical procedures needed for replacing batteries, such as those used in existing systems. - Hence, each of the
grooved electrodes 10 may form a single autonomous wireless unit adapted to independently interact with peripheral nerves, as well as with other grooved electrodes and/or other systems disposed in its vicinity. The wireless feature of thegrooved electrodes 10 may replace wire-coupled systems, thereby unrestricting patient movement. -
FIG. 2 is a perspective view of the groovedelectrode 10, in accordance with an embodiment of the present technique. In the illustrated embodiment, thegrooved electrode 10 includes a hollow elongatedrectangular body 20 forming an encasement through which electronic components can be inserted and housed. Thebody 20 hasgrooves 22 extending lengthwise throughout thebody 20. Thegrooves 22 are adapted to facilitate growth of cellular matter, i.e., peripheral nerves, about the exterior portions of the groovedelectrode 10. To facilitate optimal cellular growth, thegrooved electrode 10 may be shaped to have certain geometrical features and characteristics corresponding to those portions of anatomies in which the groovedelectrode 10 is implanted. For example, to facilitate the growth of peripheral nerves, thegrooved electrode 10 may be shaped to have a length of less than two millimeters with the width and the height being much smaller than its length. Such dimensional characteristics of the groovedelectrode 10 may correspond to the length of an active current zone generated during a peak spike phase of an active nerve fiber, as may be appreciated to those skilled in the art. In accordance with the present technique, this enables the groovedelectrode 10 to have sufficient contact with peripheral nerve fibers growing along the groovedelectrode 10, thereby providing robust signal-sampling capabilities during the peak spike phase of the nerves. It should be appreciated that thegrooved electrode 10 may attain shapes and sizes other than the one illustrated byFIG. 1 , such as those for accommodating implantation of the groove electrode through various portions of the body 12 (FIG. 1 ). - Further, the
body 20 of the groovedelectrode 10 may be formed of a biocompatible polymer adapted to seal and insulate components and/or devices, i.e., transponder (FIG. 4 ), encased within thebody 20. Such a polymer may include FDA-approved polymer materials, such as polymethylmethacrylate (PMMA), polydimethylsiloxane (PDMS), polytetraflouroethylene (PTFE), parylene, as well as biocompatible forms of polyurethane or polycarbonate. These and other envisioned materials from which thebody 20 may be made are adapted to promote growth and fusion of axons along the exterior portions of the groovedelectrode 10. - As further illustrated, the
grooved electrode 10 includes anopening 24 disposed at one of thebody 20 through which the microtransponder (FIG. 4 ) is fitted. Once peripheral nerve fibers grow lengthwise along thegrooves 22, a configuration is achieved whereby the peripheral nerves encase the transponder disposed within thebody 20. Further, electrode leads 26 disposed along thegrooves 22 are adapted to electrically connect axons of the peripheral nerves growing along thegrooves 22 with the transponder encased within thebody 20. In this manner, the transponder may form an interface capable of sensing or stimulating those axons disposed directly in the vicinity of thegroove electrode 10. In addition, thegrooved electrode 10 may be coupled to wire leads 30, configured to electrically couple thegrooved electrode 10 to external devices, such as other grooved electrodes. Accordingly, the wire leads 30 may be adapted for delivering power to components disposed within the grooved electrode. The wire leads 30 are also adapted to transfer electrical signals, such as those generated by neurons, or those used for stimulating the neurons of a peripheral nerve. In other exemplary embodiments, the aforementioned functionalities could also be achieved by using wireless techniques, as explained further below. - To optimize the interface between the peripheral nerves and components disposed within the grooved
electrode 10, thegrooves 22 may be carved throughout four edges of the groovedelectrode 10. As shown inFIG. 3 , which is a front cross-section ofFIG. 2 taken along line 3-3, each of thegrooves 22 and thebody 20 houses theelectrode lead 26, which extends lengthwise along thegrooves 22. As further illustrated, theelectrode lead 26 may be embedded within thebody 20 such that a portion of theelectrode lead 26 may be fully engulfed by thebody 20, while a remaining portion of theelectrode lead 26 may be exposed to an opening formed by thegroove 22. The electrode leads 26 are adapted to contact thoseaxons 28 growing along the opening of thegrooves 22, thereby forming an electrical connection between the axons and contact leads of a neural micro-transponder disposed within the groovedelectrode 10. This electrical connection permits electrical current to flow between theneural axons 28 and the transponder as, for example, may occur during detection of spike signals. In an exemplary embodiment, electrode leads 26 may be made from conductive carbon nanotube or other nano-scale structures having neurotrophic properties. In other embodiments, electrode leads 26 may be made from electrically conductive, biocompatible, and corrosion-resistant materials including metallic alloys, such as medical-grade stainless steel, gold, platinum, and/or a combination thereof. Other suitable materials from which the electrode leads 26 may be formed include inert-non-metallic conductors, such as graphite or polymer composites. - As illustrated by
FIG. 3 , thegrooves 22 are carved along thebody 20 in a manner permitting proper growth of theaxons 28 lengthwise within the groove along the exterior portions of the groovedelectrode 10. In addition, to promote suitable electrical contacts between theaxons 28 and the electrode leads 26, thegrooves 22 may be shaped to have certain dimensional characteristics. For example, thegrooves 22 may be carved so as to permit healthy maturation of at least one nerve fiber. At the same time, thegrooves 22 may be carved to be small enough for minimizing the number of fibers exposed to theelectrode lead 26. In an exemplary embodiment, the aforementioned attributes may be achieved by fabricating thegrooves 22 to be approximately 10 micrometers in depth and width. - As further illustrated by
FIG. 3 , the opening defined by each of thegrooves 22 may be shaped to have a unique profile. For example, the opening of thegroove 22 may be profiled to have a U, V, or rectangular shape. For example, the illustrated V-shaped profile may render the opening of each of thegrooves 22 to be approximately 15 micrometers wide, tapering down to approximately 5 micrometers at the exposed electrode surface at the floor or fundus of the groove. It should be born in mind that the openings of thegrooves 22 may be shaped to accommodate varying needs, as prescribed by physiological, anatomical, and/or clinical constraints. - Further, in accordance with the above-mentioned characteristics and profiles of
grooves 22, thegrooved electrode 10 may be configured to optimally contact and stimulate individual nerve fibers that grow along thegrooves 22. Particularly, the above-mentioned design of thegrooves 22 is adapted to permit unrestrained fiber growth, thereby eliminating risks of long-term fiber damage, such as those that are associated with existing ‘sieve’ designs. Further, thegrooves 22 are adapted to isolate fewer fibers that make contact with eachelectrode lead 26, thereby providing finer stimulus resolution and more discrete detection of fiber activity. In addition, the groove may be filled with neurotrophic factors or other biochemicals that guide or otherwise facilitate fiber growth in direct contact with theconductive electrode lead 26 along recessed portions forming the floor of the groove. -
FIG. 4 is an exploded perspective view of the groovedelectrode 10 fitted with a wireless neuro-microtransponder 40, in accordance with an embodiment of the present technique. As illustrated, thetransponder 40 is adapted to fit within the groovedelectrode 10 through theopening 24. Thetransponder 40 may be inserted within the groovedelectrode 10 together with slow releasing neurotrophic substances and anti-inflammatory gels for minimizing aversive tissue reactions and for promoting the proper implantation of the groovedelectrode 10 within the body. In this manner, thegrooved electrode 10 and thetransponder 40 make up a module adapted to physically, electrically, and chemically interact with peripheral nerves located in the vicinity of the groovedelectrode 10. Specifically, axons of peripheral nerves growing along exterior portions of the groovedelectrode 10, as facilitated by thegrooves 22, may electrically interface with thetransponder 40 via theelectrode lead 26. This configuration enables signals to propagate between thetransponder 40 and peripheral nerves. Further, thetransponder 40 includes wireless components adapted to communicate with systems external to the body, thereby enabling such systems to transmit and receive signals to or from the peripheral nerves within the body in which the groovedelectrode 10 is implanted. - The
transponder 40 includes amagnetic core 42 about which microcoils 44 are coiled. The microcoils 44 form an inductor adapted to magnetically interact with electromagnetic fields, such as those propagating from sources external to the groovedelectrode 10. In this manner, themicrocoils 44 enable thetransponder 40 to receive and/or transmit signals from or to the external systems with which thetransponder 40 communicates. In addition, themicrocoils 44 are adapted to power thetransponder 40 through power induction. In other words, themicrocoils 44 are adapted to received RF signals and convert those into electrical signals used to electrically power components of thetransponder 40. In this manner, thetransponder 40 may operate while being battery-free for extended periods of time. - The core 42 may be fabricated out of nano-crystalline magnetic alloys, adapted for achieving a high inductance (L) at radio frequencies. In the illustrated embodiment, the
coils 44 may have an (L) value four orders of magnitude greater than (L) values achieved by inductors formed of conventional materials. Further, each coil of thecoils 44 may be fabricated to have a diameter that is as small as 100 micrometers, thereby producing an inductance of approximately 10 nano-Henry. The core 42 may be fabricated using laser machining methods of nano-crystalline materials, such as cobalt. Fabrication of thecoils 44 may also involve employing techniques used in production of micro-electromechanical systems (MEMS) and nano-electromechanical systems (NEMS). - The
transponder 40 further includes aportion 46 adapted to encapsulate circuitry of the microtransponder. Theportion 46 also includes contact leads, which connect between the circuitry and thegrooved electrodes 10. As will be discussed further below, the circuitry encapsulated by theportion 46 includes electrical components adapted to sense and/or stimulate the peripheral nerves interfacing with thegrooved electrode 10. For example, theportion 46 includes identification (ID) circuitry adapted to generate unique RF signals in response to the neural spike signals generated by the peripheral nerves. This Radio Frequency Identification (RFID) capability of thetransponder 40 is configured to relay neurological activity occurring within the body to systems external to the body. The ID information may also be used to distinguish between a plurality of transponders emitting RF signals simultaneously from their respective grooved electrodes implanted within thebody 12, as shown inFIG. 1 . - Further, the
portion 46 may be coated with conductive materials, such as gold or other biocompatible conductors, to form the electrical connection between the circuitry encapsulated by theportion 46 and the electrode leads 26 disposed within thegrooves 22 of the groovedelectrode 10. Thetransponder 40 further includes acapacitor 48 disposed at the rear portion of thetransponder 40. Thecapacitor 48 may be made from a plurality of nano-tube super capacitors, adapted to increase the capacitance (C) of thetransponder 40. Thecapacitor 48 and thecoils 44 form an inductor-capacitor (LC) circuit adapted to modulate received RF signals for producing the RFID signal of thetransponder 40. -
FIG. 5 is a schematic diagram of acircuit 60 disposed within the neuro-microtransponder 40, in accordance with an embodiment of the present technique. Thecircuit 60 includes electrical components adapted to electrically interface with neurons of peripheral nerves, such as those disposed along thegrooves 22 of the groovedelectrode 10, discussed hereinabove with relation toFIGS. 2-3 . Thecircuit 60 further includes electrical components, which enable thetransponder 40 to wirelessly interact with systems external to thetransponder 40. Such systems may include other transponders implanted within the body or external coils and/or a receiver, such as those shown inFIGS. 1 and 6 , respectively. The wireless capabilities of thecircuit 60 enable the delivery of electrical signals to or from the peripheral nerves. These include electrical signals indicative of neural spike signals and/or signals configured to stimulate the peripheral nerves. - Accordingly, the
circuit 60 includes thecoils 44 coiled about acentral axis 62. Thecoil 44 is coupled in parallel to acapacitor 61 and to astimulus trigger demodulator 63, which in turn is coupled to anRF identity modulator 67 via aswitch 65. Further, theRF identity modulator 67 is coupled to arectifier 64, which in turn is coupled to aspike sensor 66 and to astimulus drive 70. Therectifier 64 and thespike sensor 66 are both coupled in parallel to acapacitor 48. In addition, thespike sensor 66 is coupled to contactlead 68, thereby electrically connecting thespike sensor 66 to theaxon 28. Similarly,contact lead 71 connects thestimulus driver 70 to theaxon 28. Thespike sensor 66 is made up of one or more field effect transistors (FET). As will be appreciated by those of ordinary skilled in the art, the FET may include metal oxide semiconductors field effect transistors (MOSFETS), such as those fabricated using standard small scale or very large scale integration (VLSI) methods. Further, thespike sensor 66 is coupled to theRF identity modulator 67, which is adapted to modulate an in coming/carrier RF signal in response to neural spike signals detected by thespike sensor 66. The contact leads 68 and 71 to which thesensor 66 and thestimulus driver 70 are connected, respectively, may be part of the portion 46 (FIG. 4 ), adapted to interface with theaxon 28 of the peripheral nerve disposed along the grooved electrode 10 (FIG. 2 ). - One configuration of the above components depicted by
FIG. 5 enables the neuro-microtransponder 40 to operate as an autonomous wireless unit, capable of detecting spike signals generated by peripheral nerves, and relaying such signals to external receivers for further processing. It should be born in mind that thetransponder 40 performs such operations while being powered by the external RF signals. The above-mentioned capabilities are facilitated by the fact that magnetic fields are not readily attenuated by human tissue. This enables the RF signals to sufficiently penetrate the human body so that signals can be received and/or transmitted by thetransponder 40. In other words, thecoils 44 are adapted to magnetically interact with the RF field whose magnetic flux fluctuates within the space encompassed by thecoils 44. By virtue of being an inductor, thecoils 44 convert the fluctuations of the magnetic flux of the external RF field into alternating electrical current, flowing within thecoils 44 and thecircuit 60. The alternating current is routed, for example, via thecoils 44 into therectifier 64, adapted to convert the alternating current into direct current. The direct current may then be used to charge thecapacitor 48, thereby creating a potential difference across the FET of the sensor trigger. - In an exemplary embodiment, a gate of the
FET 66 may be coupled via acontact lead 68 to theaxon 28. The gate of the FET may be chosen to have a threshold voltage that is within a voltage range of those signals produced by the neural axons. In this manner, during spike phases of the neural axons, the gate of theFET 66 becomes open, thereby closing thecircuit 60. Once thecircuit 60 closes, the external RF field, theinductor 44, and thecapacitor 48 induce an LC response, which modulates the external RF field with a unique modulating frequency. The LC characteristic of thecircuit 60, as well as the threshold voltage of the gate ofFET 66, can be chosen to determine the unique modulation, thereby providing a desired ID signal for thetransponder 40. Accordingly, theFET 66 provides theRF identity modulator 67 with a trigger signal for generating desired RF signal. The ID signal may indicate the nature of the neural activity in the vicinity of thetransponder 40, as well as the location of the neural activity within the body. It should be appreciated that the RF capabilities, as discussed above with respect to thecircuit 60, render the neuro-microtransponder a passive device that reacts to incoming carrier RF signals. That is, thecircuit 60 does not actively emit any signals, but rather reflects and/or scatters the electromagnetic signals of the carrier RF wave to provide signals having specific modulation. In so doing, thecircuit 60 draws power from the carrier RF wave for powering the electrical components forming thecircuit 60. - While the above-mentioned components illustrated in
FIG. 5 may be used to receive signals from the transponder 40 (FIG. 4 ) in response, to spike signals generated by peripheral nerves, other components of thecircuit 60 of thetransponder 40 may include components for stimulating the peripheral nerves using the external RF signals. For example, the RF signals received by thecoils 44 may be converted to electrical signals, via thestimulus trigger modulator 63, so as for providing sufficient current and voltage for stimulating the peripheral nerves. Hence, thestimulus trigger demodulator 63 derives power from an RF carrier signal for powering thestimulus driver 70, which delivers electrical signals suitable for stimulating theaxons 28. This may be used to treat nerves that are damaged or that are otherwise physiologically deficient. -
FIG. 6 is a schematic diagram of asystem 80 used for interfacing cellular matter, in accordance with an embodiment of the present technique. Thesystem 80 is adapted to wirelessly interface with cellular matter, such as peripheral nerves. Thesystem 80 is further adapted to receive signals, such as neural spike signals, generated by the peripheral nerves, and analyze those signals to provide feedback and/or treatment to other biological and/or biomechanical systems to which thesystem 80 is additionally coupled. In the illustrated embodiment, thesystem 80 includes the neuro-microtransponder 40 interfacing with cellular matter, such as theaxon 28 of a peripheral nerve, in a manner described and illustrated hereinabove and shown inFIGS. 1-5 . While the present exemplary embodiments may show thesingle transponder 40 coupled to theaxon 28, other embodiments may include thetransponder 40 coupled to more than a single neuron and/or a plurality transponders coupled to a plurality of neurons, some of which may or may not be in close proximity to one another. - The
system 80 further includes thecoil 19 disposed in the vicinity of thetransponder 40 and theneuron 28. Thecoil 19 is coupled to an RF signal generator and receiver (RFGRC) 82, which is coupled to aspectrum analyzer 84. Thespectrum analyzer 84 is coupled to aprocessor 86, which is also coupled to theRFGRC 82. TheRFGRC 82 provides an external RF signal, such as 100 MHz, for powering thetransponder 40 and for enabling thetransponder 40 to modulate the external RF signal so as to produce an ID signal. In an exemplary embodiment, the modulation frequency produced by thetransponder 40 may be two orders of magnitude less than the original RF signal; however, this may vary depending on the type of cellular matter interfaced and the type of transponders used. In embodiments where a plurality of transponders may be employed, a modulation frequency of approximately 1 MHz provides a relatively high bandwidth for the ID signal. This enables thesystem 80 to distinguish between relatively large amounts of neural-microtransponders responding to electrical neural signals, some of which may be closely coincident. - Further, the
RFGRC 82 receives the modulated RF signal and forwards the signal to thespectrum analyzer 84 for analysis. The spectrum analyzer is adapted to determine the modulation frequency, which is then provided to theprocessor 86 adapted to determine the ID signal characteristic of the spike signal detected by thetransponder 40. In response to the identified spike signals, theprocessor 86 may prompt theRFGRC 82 to generate RE signals adapted to stimulate other biological and/or biomechanical systems to which additional transponders may be coupled. For example, the modulated RF signal received by theRFGRC 82 may originate from neural spike signals generated by peripheral nerves that are severed or are otherwise damaged. In response to such signals, theprocessor 86 may prompt theRFGRC 82 to actuate biomechanical devices, such as those incorporated into prosthetics, thereby inducing movement. The capabilities provided by thesystem 80 for interfacing cellular matter also facilitate treatment of various neurological conditions some of which may include acute pain and obstructive sleep apnea. - Further, in another exemplary embodiment, the configuration provided by the
system 80 may be adapted to generate load modulation in thetransponder 40 by switching the drain-source resistance of the FET of thecircuit 60. This configures thecircuit 60 to detect the carrier signal. As mentioned above, in other embodiment thesystem 80 may be used for stimulating the peripheral nerves. Hence, the carrier wave emitted by theexternal coil 19 may provide thetransponder 40 with power for triggering electrodes adapted to deliver electrical signals to the peripheral nerves. In this mode of operation, the powering of thetransponder 40 and, thereafter, the stimulation of the peripheral nerves may occur in a periodic sequence in accordance with a specific frequency. -
FIGS. 7 and 8 are perspective and front views, respectively, of another exemplary embodiment of grooved electrodes, in accordance with the present technique. Accordingly,grooved electrode 100 may be made up from asubstrate 102 conformed to a hollow cylinder populated withgrooves 104 extending lengthwise along the interior portion of the cylinder. As illustrated byFIG. 8 ,grooved electrode 100 includes electrode leads 106 having a diameter less than 50 micrometers, disposed within thegrooves 104. Similar to the electrode leads 26 discussed above, theelectrodes 106 are adapted to contact axons growing along thegrooves 22, thereby forming an electrical connection between the axons and neural micro-transponders, which may be exterior to thegrooved electrode 100. The electrode leads 106 may be made from conductive carbon nanotubes, having neurotrophic properties, or from electrically conductive, biocompatible, and corrosion-resistant materials including metallic alloys. Such alloys may include medical-grade stainless steel, gold, platinum, and/or a combination thereof. Other suitable materials from which theelectrode 106 may be formed include inert-non-metallic conductors such as graphite or polymer composites. - The
grooved electrode 100 can be constructed by initially embedding a layer of theelectrodes 106 within a pre-foldedflat substrate 102 formed by casting a biocompatible polymer, such as sylgard. Thereafter, thegrooves 104 are carved through thesubstrate 102, thereby exposing a portion of each the electrode leads 106, as illustrated inFIG. 8 . Thereafter, thesubstrate 102 is rolled into a cylindrical structure forming thegrooved electrode 100. This configuration enables neural fibers to grow and fuse with the interior portions of thegrooved electrode 100. To maximize likelihood that the fibers growing along thegrooves 104 properly contact the electrode leads 106, thegrooves 104 may be filled with biochemical factors promoting fiber growth along thegrooved electrode 100, as well as adhesion thereto. The cylindrical structure provided by thegrooved electrode 100 can further facilitate formation of artificial fascicles which otherwise form internal structures of peripheral nerves, as appreciated to those skilled in the art. -
FIGS. 9 and 10 are perspective and front views, respectively, of another exemplary embodiment of grooved electrodes, in accordance with the present technique. Accordingly,grooved electrode 150 is similar to thegrooved electrode 100 discussed hereinabove in that bothgrooved electrodes grooved electrode 150 is fabricated to form a flattened structure that avoids structural failures which otherwise may result from rolling or flexing thesubstrate 102. The flattened structure of thegrooved electrode 150 may be used to force the fibers in fascicles to grow in contact with theelectrode 106. This may be done, for example, by flattening thegrooved electrode 150 to a thickness less than the fascicles, e.g., <0.3 millimeter. - Similarly, other embodiments may include grooved electrodes having various shapes and configurations adapted to promote growth of cellular matter along the body of the grooved electrodes. For example, rather than disposing electrodes, such as the
electrode 106, along the interior volume of the grooved electrodes (FIG. 710 ), theelectrodes 106 can be disposed along exterior portions of the grooved electrodes. Such exemplary embodiments may correspond to, for example, folding thesubstrate 102 so that thegrooves 104 face outward. Thus, the grooves can promote growth of peripheral nerves along the outer portions of the grooved electrode. In addition, this configuration may be implemented to produce grooved electrodes having other geometrical shapes, such as of the grooved electrodes shown inFIGS. 9 and 10 . -
FIG. 11 is a block diagram of amethod 200 for interfacing cellular matter, in accordance with an embodiment of the present technique. Themethod 200 may be used to wirelessly interface peripheral nerves using devices, such as thegrooved electrode 10,transponder 40, andsystem 80 discussed hereinabove and shown inFIGS. 2-4 and 6. Accordingly, the method begins atstep 202 in which an RF signal is generated exterior to the cellular matter. Atstep 204, the RF signal is received by a transponder implanted within the cellular matter. The RF signal is adapted to power the transponder so that it can electrically interface with the cellular matter. Atstep 206, electrical signals generated by the cellular matter are detected by the powered transponder. The electrical signals generated by the cellular matter may originate from neural spike signals of peripheral neurons interfacing with the transponder. As discussed above, the ability to detect such spike signals is facilitated by powering the transponder via the RF signal. Thereafter, the method proceeds to step 208, whereby the RF signal is modulated in response to the detection of the electrical signal produced by the peripheral nerves. The modulation of the RF may be unique insofar as it may identify the nature of the signal generated by the cellular matter and/or indicate its origin. Atstep 210, the modulated RF signal is received and, thereafter, atstep 212 the signal is analyzed to determine its ID characteristics. Thereafter, the modulated signal is processed to determine whether to generate additional RF signals to provide additional detection or stimulation of the peripheral nerves, whereby themethod 200 returns to step 202. - While only certain features of the invention have been illustrated and described herein, many modifications and changes will occur to those skilled in the art. It is, therefore, to be understood that the appended claims are intended to cover all such modifications and changes as fall within the true spirit of the invention.
Claims (19)
1. A method for treating pain, comprising:
implanting a neurostimulation device having a housing and an electrode, wherein the neurostimulation device is implanted so that the electrode is proximate to a peripheral nerve;
transmitting electromagnetic signals to the implanted neurostimulation device; and
generating a stimulation charge on the electrode to stimulate the peripheral nerve, thereby causing paresthesia that reduces pain,
wherein the housing is approximately the length of an active current zone of a peak spike phase of the peripheral nerve.
2. The method of claim 1 , wherein the electromagnetic signals are transmitted inductively.
3. The method of claim 1 , wherein the housing is less than two millimeters long.
4. The method of claim 1 , wherein the housing includes a groove.
5. The method of claim 4 , wherein the electrode is within the groove.
6. The method of claim 1 , wherein the housing has an outer surface formed of a biocompatible material.
7. The method of claim 6 , wherein the biocompatible material is polymethyl-methacrylate (PMMA), polydimethylsiloxane (PDMS), polytetrafluoroethylene (PTFE), parylene, polyurethane of polycarbonate, or combinations thereof.
8. The method of claim 4 , wherein the groove extends along an outer portion of the housing.
9. The method of claim 4 , wherein the groove extends along an inner portion of the housing.
10. The method of claim 5 , wherein the electrode is disposed along a recessed floor of the groove, wherein the groove is configured to facilitate the growth of nerve fibers for electrically interfacing the electrodes.
11. The method of claim 1 , wherein the electrode is formed of carbon nano-tubes.
12. The method of claim 4 , wherein the groove is partially filled with neurotrophic factors for promoting growth of peripheral nerves along the electrode.
13. The method of claim 4 , wherein wire leads extend from the housing, and wherein the wire leads are configured to electrically connect the housing to systems external to the housing.
14. A method comprising:
providing instructions to implant a neurostimulation device having a housing and an electrode into a person,
wherein the neurostimulation device is implanted so that the electrode is proximate to a peripheral nerve in the person,
wherein the housing is approximately the length of an active current zone of a peak spike phase of the peripheral nerve, and
wherein the neurostimulation device is configured to receive electromagnetic signals from an external device and generate a stimulation charge on the electrode to stimulate the peripheral nerve, thereby causing paresthesia that reduces pain.
15. The method of claim 14 , wherein the electromagnetic signals are transmitted inductively, wherein the housing is less than two millimeters long, wherein the housing includes a groove, wherein the electrode is within the groove, wherein the housing has an outer surface formed of a biocompatible material comprising polymethylmethacrylate (PMMA), polydimethylsiloxane (PDMS), polytetrafluoroethylene (PTFE), parylene, polyurethane of polycarbonate, or combinations thereof, wherein the electrode is disposed along a recessed floor of the groove, wherein the groove is configured to facilitate the growth of nerve fibers for electrically interfacing the electrodes, wherein the electrode is formed of carbon nano-tubes, wherein the groove is partially filled with neurotrophic factors for promoting growth of peripheral nerves along the electrode, wherein wire leads extend from the housing, and wherein the wire leads are configured to electrically connect the housing to systems external to the housing.
16. A method comprising:
transmitting electromagnetic signals to a neurostimulation device,
wherein the neurostimulation device has a housing and an electrode,
wherein the neurostimulation device is implanted in a body such that the electrode is proximate to a peripheral nerve in the body,
wherein the housing is approximately the length of an active current zone of a peak spike phase of the peripheral nerve, and
wherein the neurostimulation device is configured to receive the electromagnetic signals and generate a stimulation charge on the electrode to stimulate the peripheral nerve, thereby causing paresthesia that reduces pain.
17. The method of claim 16 , wherein the electromagnetic signals are transmitted inductively, wherein the housing is less than two millimeters long, wherein the housing includes a groove, wherein the electrode is within the groove, wherein the housing has an outer surface formed of a biocompatible material comprising polymethylmethacrylate (PMMA), polydimethylsiloxane (PDMS), polytetrafluoroethylene (PTFE), parylene, polyurethane of polycarbonate, or combinations thereof, wherein the electrode is disposed along a recessed floor of the groove, wherein the groove is configured to facilitate the growth of nerve fibers for electrically interfacing the electrodes, wherein the electrode is formed of carbon nano-tubes, wherein the groove is partially filled with neurotrophic factors for promoting growth of peripheral nerves along the electrode, wherein wire leads extend from the housing, and wherein the wire leads are configured to electrically connect the housing to systems external to the housing.
18. A method comprising:
receiving, by a stimulation device, electromagnetic signals from an external device; and
generating, by the stimulation device, a stimulation charge on an electrode to stimulate a peripheral nerve, thereby causing paresthesia that reduces pain,
wherein the neurostimulation device has a housing and the electrode,
wherein the neurostimulation device is implanted so that the electrode is proximate to the peripheral nerve, and
wherein the housing is approximately the length of an active current zone of a peak spike phase of the peripheral nerve.
19. The method of claim 18 , wherein the electromagnetic signals are transmitted inductively, wherein the housing is less than two millimeters long, wherein the housing includes a groove, wherein the electrode is within the groove, wherein the housing has an outer surface formed of a biocompatible material comprising polymethylmethacrylate (PMMA), polydimethylsiloxane (PDMS), polytetrafluoroethylene (PTFE), parylene, polyurethane of polycarbonate, or combinations thereof, wherein the electrode is disposed along a recessed floor of the groove, wherein the groove is configured to facilitate the growth of nerve fibers for electrically interfacing the electrodes, wherein the electrode is formed of carbon nano-tubes, wherein the groove is partially filled with neurotrophic factors for promoting growth of peripheral nerves along the electrode, wherein wire leads extend from the housing, and wherein the wire leads are configured to electrically connect the housing to systems external to the housing.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US13/298,185 US20120065701A1 (en) | 2007-06-25 | 2011-11-16 | Grooved Electrode and Wireless Microtransponder System |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/821,678 US7630771B2 (en) | 2007-06-25 | 2007-06-25 | Grooved electrode and wireless microtransponder system |
US12/624,383 US20100069994A1 (en) | 2007-06-25 | 2009-11-23 | Methods of inducing paresthesia using wireless neurostimulation |
US13/298,185 US20120065701A1 (en) | 2007-06-25 | 2011-11-16 | Grooved Electrode and Wireless Microtransponder System |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/624,383 Continuation US20100069994A1 (en) | 2007-06-25 | 2009-11-23 | Methods of inducing paresthesia using wireless neurostimulation |
Publications (1)
Publication Number | Publication Date |
---|---|
US20120065701A1 true US20120065701A1 (en) | 2012-03-15 |
Family
ID=40137320
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/821,678 Active 2028-01-22 US7630771B2 (en) | 2007-06-25 | 2007-06-25 | Grooved electrode and wireless microtransponder system |
US12/624,383 Abandoned US20100069994A1 (en) | 2007-06-25 | 2009-11-23 | Methods of inducing paresthesia using wireless neurostimulation |
US13/298,185 Abandoned US20120065701A1 (en) | 2007-06-25 | 2011-11-16 | Grooved Electrode and Wireless Microtransponder System |
Family Applications Before (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/821,678 Active 2028-01-22 US7630771B2 (en) | 2007-06-25 | 2007-06-25 | Grooved electrode and wireless microtransponder system |
US12/624,383 Abandoned US20100069994A1 (en) | 2007-06-25 | 2009-11-23 | Methods of inducing paresthesia using wireless neurostimulation |
Country Status (4)
Country | Link |
---|---|
US (3) | US7630771B2 (en) |
AU (1) | AU2008268368B2 (en) |
DE (1) | DE112008001669T5 (en) |
WO (1) | WO2009003025A2 (en) |
Cited By (22)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8755893B2 (en) | 2010-06-08 | 2014-06-17 | Bluewind Medical Ltd. | Tibial nerve stimulation |
US9186504B2 (en) | 2010-11-15 | 2015-11-17 | Rainbow Medical Ltd | Sleep apnea treatment |
US9457186B2 (en) | 2010-11-15 | 2016-10-04 | Bluewind Medical Ltd. | Bilateral feedback |
US9597521B2 (en) | 2015-01-21 | 2017-03-21 | Bluewind Medical Ltd. | Transmitting coils for neurostimulation |
US9643022B2 (en) | 2013-06-17 | 2017-05-09 | Nyxoah SA | Flexible control housing for disposable patch |
US9713707B2 (en) | 2015-11-12 | 2017-07-25 | Bluewind Medical Ltd. | Inhibition of implant migration |
US9764146B2 (en) | 2015-01-21 | 2017-09-19 | Bluewind Medical Ltd. | Extracorporeal implant controllers |
US9782589B2 (en) | 2015-06-10 | 2017-10-10 | Bluewind Medical Ltd. | Implantable electrostimulator for improving blood flow |
US9849289B2 (en) | 2009-10-20 | 2017-12-26 | Nyxoah SA | Device and method for snoring detection and control |
US9855032B2 (en) | 2012-07-26 | 2018-01-02 | Nyxoah SA | Transcutaneous power conveyance device |
US9861812B2 (en) | 2012-12-06 | 2018-01-09 | Blue Wind Medical Ltd. | Delivery of implantable neurostimulators |
US9943686B2 (en) | 2009-10-20 | 2018-04-17 | Nyxoah SA | Method and device for treating sleep apnea based on tongue movement |
US10004896B2 (en) | 2015-01-21 | 2018-06-26 | Bluewind Medical Ltd. | Anchors and implant devices |
US10052097B2 (en) | 2012-07-26 | 2018-08-21 | Nyxoah SA | Implant unit delivery tool |
US10105540B2 (en) | 2015-11-09 | 2018-10-23 | Bluewind Medical Ltd. | Optimization of application of current |
US10124178B2 (en) | 2016-11-23 | 2018-11-13 | Bluewind Medical Ltd. | Implant and delivery tool therefor |
US10653888B2 (en) | 2012-01-26 | 2020-05-19 | Bluewind Medical Ltd | Wireless neurostimulators |
US10751537B2 (en) | 2009-10-20 | 2020-08-25 | Nyxoah SA | Arced implant unit for modulation of nerves |
US10814137B2 (en) | 2012-07-26 | 2020-10-27 | Nyxoah SA | Transcutaneous power conveyance device |
US11213685B2 (en) | 2017-06-13 | 2022-01-04 | Bluewind Medical Ltd. | Antenna configuration |
US11253712B2 (en) | 2012-07-26 | 2022-02-22 | Nyxoah SA | Sleep disordered breathing treatment apparatus |
US11400299B1 (en) | 2021-09-14 | 2022-08-02 | Rainbow Medical Ltd. | Flexible antenna for stimulator |
Families Citing this family (60)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9186511B2 (en) | 2006-10-13 | 2015-11-17 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US9205262B2 (en) | 2011-05-12 | 2015-12-08 | Cyberonics, Inc. | Devices and methods for sleep apnea treatment |
US9913982B2 (en) | 2011-01-28 | 2018-03-13 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US9744354B2 (en) | 2008-12-31 | 2017-08-29 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US8855771B2 (en) | 2011-01-28 | 2014-10-07 | Cyberonics, Inc. | Screening devices and methods for obstructive sleep apnea therapy |
WO2008048471A2 (en) | 2006-10-13 | 2008-04-24 | Apnex Medical, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
WO2009051965A1 (en) * | 2007-10-14 | 2009-04-23 | Board Of Regents, The University Of Texas System | A wireless neural recording and stimulating system for pain management |
US20110071596A1 (en) * | 2007-11-19 | 2011-03-24 | Sule Kara | Electrode contacts for a medical implant |
US8515557B2 (en) * | 2007-11-19 | 2013-08-20 | Cochlear Limited | Electrode array for a cochlear implant |
DE112008003184T5 (en) * | 2007-11-26 | 2011-01-05 | MicroTransponder, Inc., DALLAS | Pulse stimulation systems and methods for implantable transponders |
US8457757B2 (en) | 2007-11-26 | 2013-06-04 | Micro Transponder, Inc. | Implantable transponder systems and methods |
US9089707B2 (en) | 2008-07-02 | 2015-07-28 | The Board Of Regents, The University Of Texas System | Systems, methods and devices for paired plasticity |
US8340785B2 (en) * | 2008-05-02 | 2012-12-25 | Medtronic, Inc. | Self expanding electrode cuff |
CA2722982A1 (en) * | 2008-05-02 | 2009-11-05 | Medtronic, Inc. | Self expanding electrode cuff |
US8515520B2 (en) * | 2008-12-08 | 2013-08-20 | Medtronic Xomed, Inc. | Nerve electrode |
US8442641B2 (en) | 2010-08-06 | 2013-05-14 | Nano-Retina, Inc. | Retinal prosthesis techniques |
US8718784B2 (en) | 2010-01-14 | 2014-05-06 | Nano-Retina, Inc. | Penetrating electrodes for retinal stimulation |
US8706243B2 (en) | 2009-02-09 | 2014-04-22 | Rainbow Medical Ltd. | Retinal prosthesis techniques |
US8150526B2 (en) | 2009-02-09 | 2012-04-03 | Nano-Retina, Inc. | Retinal prosthesis |
US8428740B2 (en) | 2010-08-06 | 2013-04-23 | Nano-Retina, Inc. | Retinal prosthesis techniques |
DE102009011479A1 (en) * | 2009-03-06 | 2010-09-09 | Olympus Winter & Ibe Gmbh | Surgical instrument |
NL1036784C2 (en) * | 2009-03-30 | 2010-10-04 | Univ Twente | A three-dimensional bifurcating micro-channel construct for regenerative bidirectional neuro-electric interfacing. |
WO2011034939A1 (en) | 2009-09-15 | 2011-03-24 | Rush University Medical Center | Energy-releasing carbon nanotube transponder and method of using same |
US9415216B2 (en) | 2009-10-20 | 2016-08-16 | Nyxoah SA | Devices for treatment of sleep apnea |
US8321012B2 (en) | 2009-12-22 | 2012-11-27 | The Invention Science Fund I, Llc | Device, method, and system for neural modulation as vaccine adjuvant in a vertebrate subject |
CA2831062A1 (en) | 2011-01-28 | 2012-08-02 | Stimwave Technologies Incorporated | Neural stimulator system |
US8571669B2 (en) | 2011-02-24 | 2013-10-29 | Nano-Retina, Inc. | Retinal prosthesis with efficient processing circuits |
US9589580B2 (en) | 2011-03-14 | 2017-03-07 | Cochlear Limited | Sound processing based on a confidence measure |
US9220897B2 (en) | 2011-04-04 | 2015-12-29 | Micron Devices Llc | Implantable lead |
BR112013025521B1 (en) | 2011-04-04 | 2021-04-13 | Micron Devices Llc | WIRELESS IMPLANTABLE NEURAL STIMULATOR CONDUCTOR |
EP3747507B1 (en) | 2011-07-29 | 2023-11-01 | Curonix LLC | Remote control of power or polarity selection for a neural stimulator |
EP3912675A1 (en) | 2011-08-12 | 2021-11-24 | Stimwave Technologies Incorporated | Microwave field stimulator |
US8934992B2 (en) | 2011-09-01 | 2015-01-13 | Inspire Medical Systems, Inc. | Nerve cuff |
EP3403690B1 (en) | 2011-09-15 | 2020-08-05 | Stimwave Technologies Incorporated | Relay module for implant |
EP2760530B1 (en) | 2011-09-30 | 2018-10-24 | Nyxoah SA | Apparatus to control an implant |
WO2013106884A1 (en) * | 2012-01-20 | 2013-07-25 | University Of Western Sydney | An apparatus and method for facilitating treatment of tissue |
US8986337B2 (en) | 2012-02-24 | 2015-03-24 | Elwha Llc | Devices, systems, and methods to control stomach volume |
US8903502B2 (en) | 2012-05-21 | 2014-12-02 | Micron Devices Llc | Methods and devices for modulating excitable tissue of the exiting spinal nerves |
EP2900318B1 (en) * | 2012-09-28 | 2023-05-10 | EBR Systems, Inc. | Systems and devices for selectively locating implantable devices |
US9254393B2 (en) | 2012-12-26 | 2016-02-09 | Micron Devices Llc | Wearable antenna assembly |
US9370417B2 (en) | 2013-03-14 | 2016-06-21 | Nano-Retina, Inc. | Foveated retinal prosthesis |
US9730596B2 (en) | 2013-06-28 | 2017-08-15 | Stmicroelectronics, Inc. | Low power biological sensing system |
EP3031059B1 (en) * | 2013-08-08 | 2021-09-08 | Clarus Technologies Pty Ltd. | Bionic muscle |
US9474902B2 (en) | 2013-12-31 | 2016-10-25 | Nano Retina Ltd. | Wearable apparatus for delivery of power to a retinal prosthesis |
WO2015109342A2 (en) * | 2014-01-15 | 2015-07-23 | Board Of Regents, The University Of Texas System | Regenerative interface electrode |
US9331791B2 (en) | 2014-01-21 | 2016-05-03 | Nano Retina Ltd. | Transfer of power and data |
US11383083B2 (en) | 2014-02-11 | 2022-07-12 | Livanova Usa, Inc. | Systems and methods of detecting and treating obstructive sleep apnea |
CN106794339B (en) | 2014-05-12 | 2019-08-27 | 米克伦设备有限责任公司 | Remote RF power system with small size transmitting antenna |
WO2015175600A1 (en) * | 2014-05-13 | 2015-11-19 | The Cleveland Clinic Foundation | System and method for micromagnetic stimulation of the peripheral nervous system |
US9861288B2 (en) | 2014-07-11 | 2018-01-09 | Wisconsin Alumni Research Foundation | Transparent and flexible neural electrode arrays |
WO2017078819A2 (en) * | 2015-08-13 | 2017-05-11 | University Of Southern California | Cuff electrode with lysing agent |
US11246879B2 (en) | 2016-02-09 | 2022-02-15 | Tulai Therapeutics, Inc. | Methods, agents, and devices for local neuromodulation of autonomic nerves |
WO2017143185A1 (en) * | 2016-02-17 | 2017-08-24 | Verily Life Sciences Llc | Wireless implant systems for sensing and stimulating nerves |
WO2017156232A1 (en) * | 2016-03-11 | 2017-09-14 | Board Of Regents, The University Of Texas System | Apparatus and method for nerve stimulation and/or monitoring |
US10576284B2 (en) | 2016-05-10 | 2020-03-03 | Board Of Regents, The University Of Texas System | Systems and methods for switched electrode stimulation for low power bioelectronics |
US11154547B2 (en) | 2016-06-29 | 2021-10-26 | Tulavi Therapeutics, Inc. | Treatment of sepsis and related inflammatory conditions by local neuromodulation of the autonomic nervous system |
AU2018316277B2 (en) | 2017-08-11 | 2023-12-07 | Inspire Medical Systems, Inc. | Cuff electrode |
GB2565611B (en) * | 2018-01-10 | 2019-08-07 | Neuroloom Ltd | Bio-electronic interface |
WO2020010164A1 (en) | 2018-07-02 | 2020-01-09 | Corinne Bright | Methods and devices for in situ formed nerve cap |
WO2023288218A1 (en) * | 2021-07-14 | 2023-01-19 | Tulavi Therapeutics, Inc. | Methods and devices for nerve regeneration |
Family Cites Families (107)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2641259A (en) * | 1948-10-05 | 1953-06-09 | Bartow Lab Inc | Electrophysiotherapy apparatus |
US3830242A (en) * | 1970-06-18 | 1974-08-20 | Medtronic Inc | Rate controller and checker for a cardiac pacer pulse generator means |
US3750653A (en) * | 1970-09-08 | 1973-08-07 | School Of Medicine University | Irradiators for treating the body |
US3796221A (en) * | 1971-07-07 | 1974-03-12 | N Hagfors | Apparatus for delivering electrical stimulation energy to body-implanted apparatus with signal-receiving means |
US3893462A (en) * | 1972-01-28 | 1975-07-08 | Esb Inc | Bioelectrochemical regenerator and stimulator devices and methods for applying electrical energy to cells and/or tissue in a living body |
US3786817A (en) | 1972-06-01 | 1974-01-22 | Palma J | Method and apparatus for aiding severed nerves to join |
US3942535A (en) * | 1973-09-27 | 1976-03-09 | G. D. Searle & Co. | Rechargeable tissue stimulating system |
US3955560A (en) | 1974-06-10 | 1976-05-11 | Stein Richard B | Implantable neural electrode |
US3885211A (en) * | 1974-09-16 | 1975-05-20 | Statham Instrument Inc | Rechargeable battery-operated illuminating device |
US4019519A (en) * | 1975-07-08 | 1977-04-26 | Neuvex, Inc. | Nerve stimulating device |
GB1525841A (en) * | 1976-05-18 | 1978-09-20 | Hundon Forge Ltd | Drug implanters |
US4167179A (en) * | 1977-10-17 | 1979-09-11 | Mark Kirsch | Planar radioactive seed implanter |
US4361153A (en) * | 1980-05-27 | 1982-11-30 | Cordis Corporation | Implant telemetry system |
US4399818A (en) * | 1981-04-06 | 1983-08-23 | Telectronics Pty. Ltd. | Direct-coupled output stage for rapid-signal biological stimulator |
US4612934A (en) * | 1981-06-30 | 1986-09-23 | Borkan William N | Non-invasive multiprogrammable tissue stimulator |
CA1215128A (en) * | 1982-12-08 | 1986-12-09 | Pedro Molina-Negro | Electric nerve stimulator device |
US4723536A (en) * | 1984-08-27 | 1988-02-09 | Rauscher Elizabeth A | External magnetic field impulse pacemaker non-invasive method and apparatus for modulating brain through an external magnetic field to pace the heart and reduce pain |
US4592359A (en) * | 1985-04-02 | 1986-06-03 | The Board Of Trustees Of The Leland Stanford Junior University | Multi-channel implantable neural stimulator |
GB8510832D0 (en) * | 1985-04-29 | 1985-06-05 | Bio Medical Res Ltd | Electrical stimulation of muscle |
DE3689650T2 (en) | 1985-12-17 | 1994-05-26 | United States Surgical Corp | High molecular weight bioabsorbable polymers and implants thereof. |
US4661103A (en) * | 1986-03-03 | 1987-04-28 | Engineering Development Associates, Ltd. | Multiple implant injector |
NL8602043A (en) * | 1986-08-08 | 1988-03-01 | Forelec N V | METHOD FOR PACKING AN IMPLANT, FOR example AN ELECTRONIC CIRCUIT, PACKAGING AND IMPLANT. |
US4750499A (en) * | 1986-08-20 | 1988-06-14 | Hoffer Joaquin A | Closed-loop, implanted-sensor, functional electrical stimulation system for partial restoration of motor functions |
US5079600A (en) | 1987-03-06 | 1992-01-07 | Schnur Joel M | High resolution patterning on solid substrates |
US4883067A (en) * | 1987-05-15 | 1989-11-28 | Neurosonics, Inc. | Method and apparatus for translating the EEG into music to induce and control various psychological and physiological states and to control a musical instrument |
US4878913A (en) | 1987-09-04 | 1989-11-07 | Pfizer Hospital Products Group, Inc. | Devices for neural signal transmission |
DE3834667A1 (en) * | 1988-10-12 | 1990-04-19 | Klein Schanzlin & Becker Ag | FILTER DEVICE FOR A CANNED MOTOR |
US4940065A (en) | 1989-01-23 | 1990-07-10 | Regents Of The University Of California | Surgically implantable peripheral nerve electrode |
US4902987A (en) * | 1989-04-21 | 1990-02-20 | Albright Eugene A | Inductive modulator system |
US5215088A (en) | 1989-11-07 | 1993-06-01 | The University Of Utah | Three-dimensional electrode device |
GB2240718A (en) * | 1990-02-09 | 1991-08-14 | Hundon Forge Ltd | Implanting device with needle cover |
US5265624A (en) * | 1990-09-06 | 1993-11-30 | Edentec | Stimulation collar |
NL9002183A (en) * | 1990-10-08 | 1992-05-06 | Texas Instruments Holland | METHOD FOR INSERTING A TRANSPONDER IN A LIVELY. |
IT1247157B (en) | 1991-02-11 | 1994-12-12 | Fidia Spa | BIODEGRADABLE AND BIOABSORBABLE GUIDE CHANNELS TO BE USED FOR NERVE REGENERATION. |
US5335657A (en) * | 1991-05-03 | 1994-08-09 | Cyberonics, Inc. | Therapeutic treatment of sleep disorder by nerve stimulation |
US5266926A (en) * | 1991-05-31 | 1993-11-30 | Avid Marketing, Inc. | Signal transmission and tag power consumption measurement circuit for an inductive reader |
US5222494A (en) * | 1991-07-31 | 1993-06-29 | Cyberonics, Inc. | Implantable tissue stimulator output stabilization system |
US5524338A (en) | 1991-10-22 | 1996-06-11 | Pi Medical Corporation | Method of making implantable microelectrode |
US5312439A (en) * | 1991-12-12 | 1994-05-17 | Loeb Gerald E | Implantable device having an electrolytic storage electrode |
US5193539A (en) * | 1991-12-18 | 1993-03-16 | Alfred E. Mann Foundation For Scientific Research | Implantable microstimulator |
US5193540A (en) * | 1991-12-18 | 1993-03-16 | Alfred E. Mann Foundation For Scientific Research | Structure and method of manufacture of an implantable microstimulator |
US5250026A (en) * | 1992-05-27 | 1993-10-05 | Destron/Idi, Inc. | Adjustable precision transponder injector |
US5330515A (en) * | 1992-06-17 | 1994-07-19 | Cyberonics, Inc. | Treatment of pain by vagal afferent stimulation |
US5288291A (en) * | 1992-08-12 | 1994-02-22 | Datapet, Inc. | Method and apparatus for simultaneously injecting a liquid and a transponder into an animal |
US5474082A (en) * | 1993-01-06 | 1995-12-12 | Junker; Andrew | Brain-body actuated system |
GB9302335D0 (en) * | 1993-02-05 | 1993-03-24 | Macdonald Alexander J R | Electrotherapeutic apparatus |
US5363858A (en) * | 1993-02-11 | 1994-11-15 | Francis Luca Conte | Method and apparatus for multifaceted electroencephalographic response analysis (MERA) |
US5782874A (en) * | 1993-05-28 | 1998-07-21 | Loos; Hendricus G. | Method and apparatus for manipulating nervous systems |
US5593432A (en) * | 1993-06-23 | 1997-01-14 | Neuroware Therapy International, Inc. | Method for neurostimulation for pain alleviation |
US5400784A (en) | 1993-10-15 | 1995-03-28 | Case Western Reserve University | Slowly penetrating inter-fascicular nerve cuff electrode and method of using |
US5785680A (en) * | 1994-06-13 | 1998-07-28 | Texas Instruments Incorporated | Injector and object to be injected by the injector |
US5571148A (en) * | 1994-08-10 | 1996-11-05 | Loeb; Gerald E. | Implantable multichannel stimulator |
US5776171A (en) * | 1994-09-06 | 1998-07-07 | Case Western Reserve University | Functional neuromuscular stimulation system |
US5662689A (en) * | 1995-09-08 | 1997-09-02 | Medtronic, Inc. | Method and apparatus for alleviating cardioversion shock pain |
WO1997022313A1 (en) * | 1995-12-19 | 1997-06-26 | Cochlear Limited | Cochlear implant system with soft turn on electrodes |
US5833714A (en) * | 1996-01-18 | 1998-11-10 | Loeb; Gerald E. | Cochlear electrode array employing tantalum metal |
US6463328B1 (en) * | 1996-02-02 | 2002-10-08 | Michael Sasha John | Adaptive brain stimulation method and system |
WO1997029802A2 (en) * | 1996-02-20 | 1997-08-21 | Advanced Bionics Corporation | Improved implantable microstimulator and systems employing the same |
US5833603A (en) | 1996-03-13 | 1998-11-10 | Lipomatrix, Inc. | Implantable biosensing transponder |
US5702429A (en) * | 1996-04-04 | 1997-12-30 | Medtronic, Inc. | Neural stimulation techniques with feedback |
WO1997045160A1 (en) * | 1996-05-31 | 1997-12-04 | Southern Illinois University | Methods of modulating aspects of brain neural plasticity by vagus nerve stimulation |
US5938690A (en) * | 1996-06-07 | 1999-08-17 | Advanced Neuromodulation Systems, Inc. | Pain management system and method |
US5970398A (en) * | 1996-07-30 | 1999-10-19 | Micron Communications, Inc. | Radio frequency antenna with current controlled sensitivity |
US5800458A (en) * | 1996-09-30 | 1998-09-01 | Rehabilicare, Inc. | Compliance monitor for monitoring applied electrical stimulation |
US5741316A (en) * | 1996-12-02 | 1998-04-21 | Light Sciences Limited Partnership | Electromagnetic coil configurations for power transmission through tissue |
US5735887A (en) * | 1996-12-10 | 1998-04-07 | Exonix Corporation | Closed-loop, RF-coupled implanted medical device |
US5957958A (en) * | 1997-01-15 | 1999-09-28 | Advanced Bionics Corporation | Implantable electrode arrays |
JP2001513679A (en) * | 1997-02-26 | 2001-09-04 | アルフレッド イー マン ファウンデーション フォア サイエンティフィック リサーチ | Battery powered patient subcutaneous insertion device |
US6164284A (en) * | 1997-02-26 | 2000-12-26 | Schulman; Joseph H. | System of implantable devices for monitoring and/or affecting body parameters |
US6208894B1 (en) * | 1997-02-26 | 2001-03-27 | Alfred E. Mann Foundation For Scientific Research And Advanced Bionics | System of implantable devices for monitoring and/or affecting body parameters |
US5873898A (en) * | 1997-04-29 | 1999-02-23 | Medtronic, Inc. | Microprocessor capture detection circuit and method |
US5779665A (en) * | 1997-05-08 | 1998-07-14 | Minimed Inc. | Transdermal introducer assembly |
US6458157B1 (en) * | 1997-08-04 | 2002-10-01 | Suaning Gregg Joergen | Retinal stimulator |
US5925053A (en) | 1997-09-02 | 1999-07-20 | Children's Medical Center Corporation | Multi-lumen polymeric guidance channel, method for promoting nerve regeneration, and method of manufacturing a multi-lumen nerve guidance channel |
US20010027336A1 (en) * | 1998-01-20 | 2001-10-04 | Medtronic, Inc. | Combined micro-macro brain stimulation system |
US6009350A (en) * | 1998-02-06 | 1999-12-28 | Medtronic, Inc. | Implant device telemetry antenna |
US6058330A (en) * | 1998-03-06 | 2000-05-02 | Dew Engineering And Development Limited | Transcutaneous energy transfer device |
US6221908B1 (en) * | 1998-03-12 | 2001-04-24 | Scientific Learning Corporation | System for stimulating brain plasticity |
US6047214A (en) * | 1998-06-09 | 2000-04-04 | North Carolina State University | System and method for powering, controlling, and communicating with multiple inductively-powered devices |
US6181969B1 (en) * | 1998-06-26 | 2001-01-30 | Advanced Bionics Corporation | Programmable current output stimulus stage for implantable device |
US6141588A (en) * | 1998-07-24 | 2000-10-31 | Intermedics Inc. | Cardiac simulation system having multiple stimulators for anti-arrhythmia therapy |
WO2000006249A2 (en) | 1998-07-27 | 2000-02-10 | Case Western Reserve University | Method and apparatus for closed-loop stimulation of the hypoglossal nerve in human patients to treat obstructive sleep apnea |
US6240316B1 (en) * | 1998-08-14 | 2001-05-29 | Advanced Bionics Corporation | Implantable microstimulation system for treatment of sleep apnea |
US6201980B1 (en) * | 1998-10-05 | 2001-03-13 | The Regents Of The University Of California | Implantable medical sensor system |
DE69931006T2 (en) * | 1998-10-14 | 2007-01-04 | Terumo K.K. | Wired radiation source and catheter assembly for radiotherapy |
US6208902B1 (en) * | 1998-10-26 | 2001-03-27 | Birinder Bob Boveja | Apparatus and method for adjunct (add-on) therapy for pain syndromes utilizing an implantable lead and an external stimulator |
US6366814B1 (en) * | 1998-10-26 | 2002-04-02 | Birinder R. Boveja | External stimulator for adjunct (add-on) treatment for neurological, neuropsychiatric, and urological disorders |
DE19859171C2 (en) * | 1998-12-21 | 2000-11-09 | Implex Hear Tech Ag | Implantable hearing aid with tinnitus masker or noiser |
US6270472B1 (en) * | 1998-12-29 | 2001-08-07 | University Of Pittsburgh Of The Commonwealth System Of Higher Education | Apparatus and a method for automatically introducing implants into soft tissue with adjustable spacing |
WO2000038570A1 (en) * | 1998-12-31 | 2000-07-06 | Ball Semiconductor, Inc. | Miniature implanted orthopedic sensors |
WO2000040295A1 (en) * | 1999-01-06 | 2000-07-13 | Ball Semiconductor, Inc. | Implantable neuro-stimulator |
US6161030A (en) * | 1999-02-05 | 2000-12-12 | Advanced Brain Monitoring, Inc. | Portable EEG electrode locator headgear |
US6409655B1 (en) * | 1999-03-05 | 2002-06-25 | David L. Wilson | Device for applying stimuli to a subject |
US6505075B1 (en) | 1999-05-29 | 2003-01-07 | Richard L. Weiner | Peripheral nerve stimulation method |
US6456866B1 (en) * | 1999-09-28 | 2002-09-24 | Dustin Tyler | Flat interface nerve electrode and a method for use |
US6308102B1 (en) * | 1999-09-29 | 2001-10-23 | Stimsoft, Inc. | Patient interactive neurostimulation system and method |
WO2001081552A1 (en) * | 2000-04-19 | 2001-11-01 | Iowa State University Research Foundation, Inc. | Patterned substrates and methods for nerve regeneration |
US6871099B1 (en) * | 2000-08-18 | 2005-03-22 | Advanced Bionics Corporation | Fully implantable microstimulator for spinal cord stimulation as a therapy for chronic pain |
US6658300B2 (en) * | 2000-12-18 | 2003-12-02 | Biosense, Inc. | Telemetric reader/charger device for medical sensor |
EP1349608A1 (en) | 2001-01-11 | 2003-10-08 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Sieve electrode which can be connected to a nerve stump |
US20050143789A1 (en) * | 2001-01-30 | 2005-06-30 | Whitehurst Todd K. | Methods and systems for stimulating a peripheral nerve to treat chronic pain |
DE60215029T2 (en) | 2001-06-29 | 2007-10-25 | The Board Of Trustees Of The Leland Stanford Junior University, Palo Alto | ARTICLE CHIP INTERFACE CONNECTION FOR ELECTRONIC REITINAIMPLANTAT |
US6829508B2 (en) * | 2001-10-19 | 2004-12-07 | Alfred E. Mann Foundation For Scientific Research | Electrically sensing and stimulating system for placement of a nerve stimulator or sensor |
CA2491018C (en) | 2002-06-28 | 2013-06-18 | Advanced Bionics Corporation | Microstimulator having self-contained power source and bi-directional telemetry system |
US20050137652A1 (en) * | 2003-12-19 | 2005-06-23 | The Board of Regents of the University of Texas at Dallas | System and method for interfacing cellular matter with a machine |
US7245972B2 (en) * | 2004-04-29 | 2007-07-17 | Alfred E. Mann Foundation For Scientific Research | Electrical treatment to treat shoulder subluxation |
US7729758B2 (en) * | 2005-11-30 | 2010-06-01 | Boston Scientific Neuromodulation Corporation | Magnetically coupled microstimulators |
-
2007
- 2007-06-25 US US11/821,678 patent/US7630771B2/en active Active
-
2008
- 2008-06-25 WO PCT/US2008/068165 patent/WO2009003025A2/en active Application Filing
- 2008-06-25 AU AU2008268368A patent/AU2008268368B2/en not_active Ceased
- 2008-06-25 DE DE112008001669T patent/DE112008001669T5/en not_active Ceased
-
2009
- 2009-11-23 US US12/624,383 patent/US20100069994A1/en not_active Abandoned
-
2011
- 2011-11-16 US US13/298,185 patent/US20120065701A1/en not_active Abandoned
Cited By (46)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9943686B2 (en) | 2009-10-20 | 2018-04-17 | Nyxoah SA | Method and device for treating sleep apnea based on tongue movement |
US11857791B2 (en) | 2009-10-20 | 2024-01-02 | Nyxoah SA | Arced implant unit for modulation of nerves |
US11273307B2 (en) | 2009-10-20 | 2022-03-15 | Nyxoah SA | Method and device for treating sleep apnea |
US10898717B2 (en) | 2009-10-20 | 2021-01-26 | Nyxoah SA | Device and method for snoring detection and control |
US10751537B2 (en) | 2009-10-20 | 2020-08-25 | Nyxoah SA | Arced implant unit for modulation of nerves |
US10716940B2 (en) | 2009-10-20 | 2020-07-21 | Nyxoah SA | Implant unit for modulation of small diameter nerves |
US9849289B2 (en) | 2009-10-20 | 2017-12-26 | Nyxoah SA | Device and method for snoring detection and control |
US9950166B2 (en) | 2009-10-20 | 2018-04-24 | Nyxoah SA | Acred implant unit for modulation of nerves |
US8788045B2 (en) | 2010-06-08 | 2014-07-22 | Bluewind Medical Ltd. | Tibial nerve stimulation |
US8755893B2 (en) | 2010-06-08 | 2014-06-17 | Bluewind Medical Ltd. | Tibial nerve stimulation |
US9186504B2 (en) | 2010-11-15 | 2015-11-17 | Rainbow Medical Ltd | Sleep apnea treatment |
US9457186B2 (en) | 2010-11-15 | 2016-10-04 | Bluewind Medical Ltd. | Bilateral feedback |
US10653888B2 (en) | 2012-01-26 | 2020-05-19 | Bluewind Medical Ltd | Wireless neurostimulators |
US11648410B2 (en) | 2012-01-26 | 2023-05-16 | Bluewind Medical Ltd. | Wireless neurostimulators |
US12059571B2 (en) | 2012-01-26 | 2024-08-13 | Bluewind Medical Ltd | Wireless neurostimulators |
US9855032B2 (en) | 2012-07-26 | 2018-01-02 | Nyxoah SA | Transcutaneous power conveyance device |
US11730469B2 (en) | 2012-07-26 | 2023-08-22 | Nyxoah SA | Implant unit delivery tool |
US10052097B2 (en) | 2012-07-26 | 2018-08-21 | Nyxoah SA | Implant unit delivery tool |
US10814137B2 (en) | 2012-07-26 | 2020-10-27 | Nyxoah SA | Transcutaneous power conveyance device |
US11253712B2 (en) | 2012-07-26 | 2022-02-22 | Nyxoah SA | Sleep disordered breathing treatment apparatus |
US10716560B2 (en) | 2012-07-26 | 2020-07-21 | Nyxoah SA | Implant unit delivery tool |
US10918376B2 (en) | 2012-07-26 | 2021-02-16 | Nyxoah SA | Therapy protocol activation triggered based on initial coupling |
US10238863B2 (en) | 2012-12-06 | 2019-03-26 | Bluewind Medical Ltd. | Delivery of implantable neurostimulators |
US11464966B2 (en) | 2012-12-06 | 2022-10-11 | Bluewind Medical Ltd. | Delivery of implantable neurostimulators |
US11278719B2 (en) | 2012-12-06 | 2022-03-22 | Bluewind Medical Ltd. | Delivery of implantable neurostimulators |
US9861812B2 (en) | 2012-12-06 | 2018-01-09 | Blue Wind Medical Ltd. | Delivery of implantable neurostimulators |
US10512782B2 (en) | 2013-06-17 | 2019-12-24 | Nyxoah SA | Remote monitoring and updating of a medical device control unit |
US11298549B2 (en) | 2013-06-17 | 2022-04-12 | Nyxoah SA | Control housing for disposable patch |
US11642534B2 (en) | 2013-06-17 | 2023-05-09 | Nyxoah SA | Programmable external control unit |
US9643022B2 (en) | 2013-06-17 | 2017-05-09 | Nyxoah SA | Flexible control housing for disposable patch |
US10004896B2 (en) | 2015-01-21 | 2018-06-26 | Bluewind Medical Ltd. | Anchors and implant devices |
US9597521B2 (en) | 2015-01-21 | 2017-03-21 | Bluewind Medical Ltd. | Transmitting coils for neurostimulation |
US9764146B2 (en) | 2015-01-21 | 2017-09-19 | Bluewind Medical Ltd. | Extracorporeal implant controllers |
US9782589B2 (en) | 2015-06-10 | 2017-10-10 | Bluewind Medical Ltd. | Implantable electrostimulator for improving blood flow |
US10369366B2 (en) | 2015-06-10 | 2019-08-06 | Bluewind Medical Ltd. | Implantable electrostimulator for improving blood flow |
US11612747B2 (en) | 2015-11-09 | 2023-03-28 | Bluewind Medical Ltd. | Optimization of application of current |
US11116975B2 (en) | 2015-11-09 | 2021-09-14 | Bluewind Medical Ltd. | Optimization of application of current |
US10105540B2 (en) | 2015-11-09 | 2018-10-23 | Bluewind Medical Ltd. | Optimization of application of current |
US10449374B2 (en) | 2015-11-12 | 2019-10-22 | Bluewind Medical Ltd. | Inhibition of implant migration |
US9713707B2 (en) | 2015-11-12 | 2017-07-25 | Bluewind Medical Ltd. | Inhibition of implant migration |
US11439833B2 (en) | 2016-11-23 | 2022-09-13 | Bluewind Medical Ltd. | Implant-delivery tool |
US10124178B2 (en) | 2016-11-23 | 2018-11-13 | Bluewind Medical Ltd. | Implant and delivery tool therefor |
US10744331B2 (en) | 2016-11-23 | 2020-08-18 | Bluewind Medical Ltd. | Implant and delivery tool therefor |
US11213685B2 (en) | 2017-06-13 | 2022-01-04 | Bluewind Medical Ltd. | Antenna configuration |
US11951316B2 (en) | 2017-06-13 | 2024-04-09 | Bluewind Medical Ltd. | Antenna configuration |
US11400299B1 (en) | 2021-09-14 | 2022-08-02 | Rainbow Medical Ltd. | Flexible antenna for stimulator |
Also Published As
Publication number | Publication date |
---|---|
WO2009003025A3 (en) | 2009-02-19 |
AU2008268368B2 (en) | 2011-11-10 |
AU2008268368A1 (en) | 2008-12-31 |
US20080319506A1 (en) | 2008-12-25 |
US20100069994A1 (en) | 2010-03-18 |
WO2009003025A2 (en) | 2008-12-31 |
DE112008001669T5 (en) | 2010-05-12 |
US7630771B2 (en) | 2009-12-08 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7630771B2 (en) | Grooved electrode and wireless microtransponder system | |
AU2008329724B2 (en) | Transfer coil architecture | |
AU2008352005B2 (en) | Array of joined microtransponders for implantation | |
US20120296399A1 (en) | Array of Joined Microtransponders for Implantation | |
CA2671126C (en) | Equine airway disorders | |
AU2008329716B2 (en) | Implantable transponder systems and methods | |
Cho et al. | A SU-8-based fully integrated biocompatible inductively powered wireless neurostimulator | |
CA2341708A1 (en) | Medical implant system | |
Liang et al. | An implantable bi-directional wireless transmission system for transcutaneous biological signal recording | |
Cho et al. | A MEMS-based fully-integrated wireless neurostimulator | |
KR20070005982A (en) | Implantable brain activity monitoring and electrical stimulation system | |
US9538957B2 (en) | Implantable medical device that is configured for movable connection to an implanted trunk and that is able to inductively exchange signals with the trunk | |
US10575750B2 (en) | Neurotrophic electrode system | |
KR101128341B1 (en) | Cyborg systems following user's intention | |
Das et al. | Biointegrated implantable brain devices | |
AU758015B2 (en) | Medical implant system | |
Khalifa | Design, Fabrication, and Validation of a Highly Miniaturized Wirelessly Powered Neural Implant | |
Khanna et al. | Introduction, Scope, and Overview | |
Krüger | Investigation of electrodes as bidirectional human machine interface for neuro-technical control of prostheses | |
ZA200101735B (en) | Medical implant system. | |
AU2012202299A1 (en) | Equine airway disorders |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |