Abstract: A cochlear implant sound processor is powered by a rechargeable battery that is permanently integrated into the sound processor. The sound processor contains an inductive coil that may be tuned to an external charging coil for battery recharging. The electronic circuits and coil of the sound processor are housed in a material transparent to RF signals. The sound processor may be placed in a recharging base station in which the sound processor is positioned in a space surrounded by the inductive charging coil embedded in a material transparent to RF signals. The inductive charging coil sends power to the coil inside the processor and thereby recharges the battery. An alternative embodiment utilizes contacts in the sound processor case and aligned terminals in the recharging base station that allow direct charging of the battery.

Abstract: A hearing aid module is shaped for insertion into a tunnel made through the soft tissue that connects the retro-auricular space with the ear canal. The hearing aid module contains a speaker or auditory transducer, a battery or other power source powering the module, signal processing circuitry, a microphone, and a hollow tube which contains a steroid or drug. Telemetry circuitry within the module allows the signal processing circuitry to be programmed with a desired frequency response or signal processing strategy using an external programming unit. A remote control unit permits the user to make simple adjustments, such as volume and/or tone (frequency) control.

Abstract: A cochlear implant sound processor is powered by a rechargeable battery that is permanently integrated into the sound processor. The sound processor contains an inductive coil that may be tuned to an external charging coil for battery recharging. The electronic circuits and coil of the sound processor are housed in a material transparent to RF signals. The sound processor may be placed in a recharging base station in which the sound processor is positioned in a space surrounded by the inductive charging coil embedded in a material transparent to RF signals. The inductive charging coil sends power to the coil inside the processor and thereby recharges the battery. An alternative embodiment utilizes contacts in the sound processor case and aligned terminals in the recharging base station that allow direct charging of the battery.

Abstract: A cochlear implant sound processor is powered by a rechargeable battery that is permanently integrated into the sound processor. The sound processor contains an inductive coil that may be tuned to an external charging coil for battery recharging. The electronic circuits and coil of the sound processor are housed in a material transparent to RF signals. The sound processor may be placed in a recharging base station in which the sound processor is positioned in a space surrounded by the inductive charging coil embedded in a material transparent to RF signals. The inductive charging coil sends power to the coil inside the processor and thereby recharges the battery. An alternative embodiment utilizes contacts in the sound processor case and aligned terminals in the recharging base station that allow direct charging of the battery.

Abstract: An implantable microstimulator, or equivalent neural stimulator, generates a relatively simple signal containing temporally challenging information and delivers such signal to the middle or outer portion of the ear contra-lateral to an ear having a cochlear implant of a bilaterally deafened patient. Such stimulation delivered to the contra lateral ear advantageously increases the survival rate of neurons therein, and further helps maintain or extend the plasticity of the higher auditory pathways of the contra-lateral ear, thereby allowing a cochlear implant to be more effectively used in such ear at a later date. The stimulation provided by the microstimulator, or equivalent simple neural stimulator, need not be continuous, but may be provided only during limited periods of time each day, or only on selected days. Further, such stimulation preserves whatever residual hearing may be left in the contra lateral ear.

Abstract: A system and method uses an electrical stimulator to stimulate the auditory system with a relatively simple signal that contains temporally challenging information in order to preserve neuronal survival and plasticity of the auditory system, and also to preserve residual hearing. The stimulation provided need not be continuous, but may be provided only during limited periods of time each day, or only on selected days. The system or method is particularly suited for very young children who acquire hearing impairment or deafness early in life and who may not yet be ready for a cochlear implant. The invention requires only minimal surgical intervention, if any, and may be carried out without the need for intra-cochlear electrodes. Under special circumstances, the invention may also be used with older children or adults with a hearing impairment or deafness.

Abstract: A hearing aid module is shaped for insertion into a tunnel made through the soft tissue that connects the retro-auricular space with the ear canal. The hearing aid module contains a speaker or auditory transducer, a battery or other power source powering the module, signal processing circuitry, a microphone, and a hollow tube which contains a steroid or drug. Telemetry circuitry within the module allows the signal processing circuitry to be programmed with a desired frequency response or signal processing strategy using an external programming unit. A remote control unit permits the user to make simple adjustments, such as volume and/or tone (frequency) control.

Abstract: A soft, ball-shaped middle-ear electrode is inserted and wedged into the natural cavity that exists in front of the round window. An electrical pulse generator connected to the soft, ball-shaped electrode provides electrical stimulation to the region surrounding the round window for the purpose of suppressing tinnitus or to improve hearing.

Abstract: For a patient having unilateral hearing loss, an extra-cochlear electrode is placed within the middle ear of the deaf ear, and is connected to a microstimulator that is implanted under the skin or recessed in the temporal bone or some other location in the skull near the deaf ear. In one preferred embodiment, the extra-cochlear electrode is a mesh ball electrode that is placed in the round window niche, on the promontory, or in some other extra-cochlear location, of the deaf ear. Whenever a trigger signal generated by a microphone is received by the microstimulator, the microstimulator generates a stimulus pulse that is applied to the mesh ball electrode. The electrical signal applied through the mesh ball electrode provides temporal information to supplement the sound signal that is received by the other, normally-functioning ear of the patient.

Abstract: A hearing aid module is shaped for insertion into a tunnel made through the soft tissue that connects the retro-auricular space with the ear canal. The hearing aid module contains a speaker or auditory transducer, a battery or other power source powering the module, signal processing circuitry, and a microphone. Telemetry circuitry within the module allows the signal processing circuitry to be programmed with a desired frequency response or signal processing strategy using an external programming unit. A remote control unit permits the user to make simple adjustments, such as volume and/or tone (frequency) control.

Abstract: An implantable microstimulator and a stimulating electrode are implanted to treat tinnitus. The microstimulator is connected to the stimulating electrode via a short, flexible lead. The electrode is implanted in the promontory of the cochlea or in the cochlear round window niche to deliver electrical stimulation to the auditory nervous system and thereby suppress or mask the tinnitus. The microstimulator may be surgically implanted through the ear canal, via a mastoidectomy or through the middle fossa, i.e., a supra-meatal approach. The microstimulator may be placed in middle ear cavity, a bony recess created in the bone surrounding the middle ear, the mastoid, the cochlea or a part of the temporal bone. In addition, the system may further include a test electrode, a test stimulator and a remote programming device that employs a bi-directional radio-frequency communication link to control and program the microstimulator and the test stimulator.

Abstract: Exemplary methods of treating a patient with epilepsy include applying a stimulus to a stimulation site within the patient with an implanted system control unit in accordance with one or more stimulation parameters. The stimulus includes a stimulation current having a frequency substantially equal to or greater than 400 Hz. Exemplary systems for treating a patient with epilepsy include a system control unit configured to apply a stimulus to a stimulation site within the patient in accordance with one or more stimulation parameters. The stimulus includes a stimulation current having a frequency substantially equal to or greater than 400 Hz.

Abstract: A hollow tube device enclosing a personal sound link module is inserted into a tunnel (40) made through the soft tissue connecting the retro-auricular space (50) with the ear canal (30). The hollow tube device contains an acoustic transducer (65), located at the distal part (68) of an enclosed case, close to or inside the ear canal, an antenna (64) that receives and also potentially sends signals to a remote source, signal processing circuitry (67), telemetry circuitry (69), a power source (66) that powers the device, and possibly a microphone (63). Signals transmitted from a remote source are received through the antenna and telemetry circuitry, processed, and presented to the acoustic transducer, where they are converted to sound waves broadcast into the user's ear canal. The remote source may be a radio station, radio receiver, CD player, DVD player, tape player, audio system, telephone, TV receiver or station, or other source of audio signals intended to be heard privately by the user.

Abstract: Systems and methods for applying electrical stimulation to the brain to treat headaches and neuralgia use at least one implantable system control unit (SCU), specifically an implantable signal/pulse generator (IPG) with one or more electrodes. The IPG is implanted in the skull and communicates with at least one external appliance, such as a Behind-the-Ear (BTE) unit. In a preferred embodiment, the system is capable of open- and closed-loop operation. In closed-loop operation, at least one SCU includes a sensor, and the sensed condition is used to adjust stimulation parameters.

Abstract: A personal sound link module (60) is inserted into a tunnel (40) made through the soft tissue connecting the retro-auricular space (50) with the ear canal (30). The module contains an acoustic transducer (65), located at the distal part (68) of the module, close to or inside the ear canal, an antenna (64) that receives and also potentially sends signals to a remote source, signal processing circuitry (67), telemetry circuitry (69), a power source (66) that powers the module, and possibly a microphone (63). Signals transmitted from a remote source are received through the antenna and telemetry circuitry, processed, and presented to the acoustic transducer, where they are converted to sound waves broadcast into the user's ear canal. The remote source may be a radio station, radio receiver, CD player, DVD player, tape player, audio system, telephone, TV receiver or station, or other source of audio signals intended to be heard privately by the user.

Abstract: The invention is a method for increasing the airflow to a zinc-air battery such that the energy density is 500 mwh/cc to 1000 mwh/cc. This allows 8 to 16 hours use as a primary (throw-away) battery, with, for example, high-duty cycle, high-drain cochlear implants, and neuromuscular stimulators for nerves, muscles, and both nerves and muscles together. The systems incorporating the high energy density source are also part of the invention, as well as the resulting apparatus of the method. The uses of this inexpensive, i.e., a $1.00 per day, throw-away primary battery are new uses of the modified zinc-air battery and are directed toward helping people hear again, walk again, and regain body functionality which they have otherwise lost permanently.

Abstract: A method of making an implantable electrode array, adapted for insertion into a cochlea, includes the steps of: (a) forming electrode contact pieces made from a precious, biocompatible material into a desired shape; (b) attaching the electrode contact pieces to a foil sheet made from a non-toxic but chemically-active metal; (c) connecting a wiring system to the metal contact pieces; (d) molding a flexible polymer carrier around the electrode contact pieces and wiring system while such are held in place by the foil sheet; and (e) etching away the foil sheet, leaving the electrode contact pieces exposed at a surface of the molded polymer carrier. The exposed electrode contacts are made so as to have a shape, geometry, or makeup that aids in controlling the current flow and current density associated with the electrode contact as a function of position on the electrode contact.

Abstract: A hearing aid module is shaped for insertion into a tunnel made through the soft tissue that connects the retro-auricular space with the ear canal. The hearing aid module contains a speaker or auditory transducer, a battery or other power source powering the module, signal processing circuitry, and a microphone. Telemetry circuitry within the module allows the signal processing circuitry to be programmed with a desired frequency response or signal processing strategy using an external programming unit. A remote control unit permits the user to make simple adjustments, such as volume and/or tone (frequency) control.

Abstract: A hearing aid module (60) is shaped for insertion into a tunnel (40) made through the soft tissue that connects the retro-auricular space (50) with the ear canal (30). A hollow tube (44) may first be chronically or acutely implanted in such tunnel, and the hearing aid module inserted into the tube. The tube or hearing aid module may have a coating (45) containing a steroid or drug adapted to minimize infection and/or inflammation. The hearing aid module contains a speaker (65), a battery or other power source (66) powering the module, signal processing circuitry (67), and a microphone (63). Telemetry circuitry (69) within the module allows the signal processing circuitry to be programmed with a desired frequency response or signal processing strategy using an external programming unit (74). A remote control unit (75) permits the user to make simple adjustments, such as volume and/or tone control.

Abstract: A cochlear implant sound processor is powered by a rechargeable battery that is permanently integrated into the sound processor. The sound processor contains an inductive coil that may be tuned to an external charging coil for battery recharging. The electronic circuits and coil of the sound processor are housed in a material transparent to RF signals. The sound processor may be placed in a recharging base station in which the sound processor is positioned in a space surrounded by the inductive charging coil embedded in a material transparent to RF signals. The inductive charging coil sends power to the coil inside the processor and thereby recharges the battery. An alternative embodiment utilizes contacts in the sound processor case and aligned terminals in the recharging base station that allow direct charging of the battery.