Abstract: An implantable stimulator(s) with at least one infusion outlet and/or at least one electrode, is implanted with the outlet(s) and/or electrode(s) located adjacent to a pudendal nerve(s) and potentially other nerve(s) innervating the reproductive organs, such as the cavernous nerve(s). Stimulation of such nerve(s) is provided via stimulating drugs and/or electrical stimulation as a therapy for erectile dysfunction. The stimulator uses a power source/storage device, such as a rechargeable battery. Periodic recharging of such a battery is accomplished, for example, by inductive coupling with an external appliance. The stimulator provides means of stimulating a nerve(s) when desired, without the need for external appliances during the stimulation session. When necessary, external appliances are used for the transmission of data to and/or from the stimulator(s) and for the transmission of power. The system is capable of open- and closed-loop operation.

Abstract: An In The Ear (ITE) microphone improves the acoustic response of a Behind The Ear (BTE) Implantable Cochlear Stimulation (ICS) system during telephone use. An acoustic seal provided by holding a telephone earpiece against the ear provides improved coupling of low frequency (up to about 1 KHz) sound waves, sufficient to overcome losses due to the near field acoustic characteristics common to telephones. In a preferred embodiment, the ITE microphone is connected to a removable ear hook of the BTE ICS system by a short bendable stalk.

Abstract: Introducing one or more stimulating drugs to the brain and/or applying electrical stimulation to the brain is used to treat epilepsy. At least one implantable system control unit (SCU) produces electrical pulses delivered via electrodes implanted in the brain and/or drug infusion pulses delivered via a catheter implanted in the brain. The stimulation is delivered to targeted brain structures to adjust the activity of those structures. The small size of the SCUs of the invention allow SCU implantation directly and entirely within the skull and/or brain. Simplicity of the preferred systems and methods and compactness of the preferred system are enabled by the modest control parameter set of these SCU, which do not require or include a sensing feature.

Abstract: An envelope based amplitude mapping achieves the signal compression required to provide a natural sound level without the high processor loading or waveform alteration. In a preferred embodiment, the output of a family of parallel bandpass filters is processed by an envelope detector, followed by decimation. The resulting reduced data rate envelope is log mapped to produce a scaling factor for the original high data rate bandpass filter output sequence. The resulting scaled signal determines the current level for stimulation of the cochlea for each frequency band, which stimulation achieves a log mapping of the sound amplitude effect similar to natural hearing, while reducing processor load, and preserving waveform shape.

Abstract: Interelectrode impedance or electric field potential measurements are used to determine the relative orientation of one lead to other leads in the spinal column or other body/tissue location. Interelectrode impedance is determined by measuring impedance vectors. The value of the impedance vector is due primarily to the electrode-electrolyte interface, and the bulk impedance between the electrodes. The bulk impedance between the electrodes is, in turn, made up of (1) the impedance of the tissue adjacent to the electrodes, and (2) the impedance of the tissue between the electrodes. In one embodiment, the present invention makes both monopolar and bipolar impedance measurements, and then corrects the bipolar impedance measurements using the monopolar measurements to eliminate the effect of the impedance of the tissue adjacent the electrodes. The orientation and position of the leads may be inferred from the relative minima of the corrected bipolar impedance values.

Abstract: A fully implantable cochlear prosthesis includes (1) an implantable hermetically sealed case wherein electronic circuitry, including a battery and an implantable microphone, are housed, (2) an active electrode array that provides a programmable number of electrode contacts through which stimulation current may be selectively delivered to surrounding tissue, preferably through the use of appropriate stimulation groups, and (3) a connector that allows the active electrode array to be detachably connected with the electronic circuitry within the sealed case. The active electrode array provides a large number of both medial and lateral contacts, any one of which may be selected to apply a stimulus pulse through active switching elements included within the array. The active switching elements included within the array operate at a very low compliance voltage, thereby reducing power consumption.

Abstract: An implantable system control unit (SCU) includes means for measuring tissue impedance or other condition to determine allograft health, in order to predict or detect allograft rejection. The SCU also includes at least two electrodes coupled to means for delivering electrical stimulation to a patient within whom the device is implanted, and may also include a reservoir for holding one or more drugs and a driver means for delivering the drug(s) to the patient. In certain embodiments, 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. Alternatively, this sensory “SCU” sounds an alarm, communicates an alarm to an external device, and/or is responsive to queries regarding sensed information, such as tissue impedance.

Abstract: An electrode system includes an implantable electrode having at least one electrode contact, an insertion tool, and a technique or method that allows the electrode contact to be positioned within soft tissue at a selected target stimulation site.

Abstract: Systems and methods for introducing one or more stimulating drugs and/or applying electrical stimulation to the brain to at least treat or prevent obesity and/or other eating disorders uses at least one system control unit (SCU) producing electrical pulses delivered via electrodes implanted in the brain and/or producing drug infusion pulses, wherein the stimulating drug(s) are delivered to targeted areas in the brain.

Abstract: A method and system for treatment of incontinence, urgency, frequency, and/or pelvic pain includes implantation of electrodes on a lead or the discharge portion of a catheter adjacent the perineal nerve(s) or tissue(s) to be stimulated. Stimulation pulses, either electrical or drug infusion pulses, are supplied by a stimulator implanted remotely, and through the lead or catheter, which is tunneled subcutaneously between the stimulator and stimulation site. For instance, the system and method reduce or eliminate the incidence of unintentional episodes of bladder emptying by stimulating nerve pathways that diminish involuntary bladder contractions, improve closure of the bladder outlet, and/or improve the long-term health of the urinary system by increasing bladder capacity and period between emptying.

Abstract: Systems and methods for introducing one or more stimulating drugs and/or applying electrical stimulation to the brain to at least treat or prevent diabetes uses at least one system control unit (SCU) producing electrical pulses delivered via electrodes implanted in the brain and/or producing drug infusion pulses, wherein the stimulating drug(s) are delivered to targeted areas in the brain.

Abstract: A deep brain stimulation (DBS) system (10) provides a multiplicity of stimulation channels through which stimulation may be delivered deep within the brain of the patient. The DBS system is powered by a rechargeable battery (27). In one embodiment, the system has four channels driving sixteen electrodes (32). The DBS system is easily programmed for use by a clinician using a clinician programming system (60), and further affords a simple but highly advanced hand held programmer (50) control interface through which the patient may easily change stimulation parameters within acceptable limits. The DBS system (10) includes a small, implantable pulse generator (20) that is small enough to be implanted directly in the cranium of the patient, thereby eliminating the long lead wires and tunneling procedures that have been used in the past.

Abstract: An implantable pulse generator includes a current steering capability that allows a clinician or patient to quickly determine a desired electrode stimulation pattern, including which electrodes of a group of electrodes within an electrode array should receive a stimulation current, including the amplitude, width and pulse repetition rate of such current. Movement of the selected group of electrodes is facilitated through the use of remotely generated directional signals, generated by a pointing device, such as a joystick. As movement of the selected group of electrodes occurs, current redistribution amongst the various electrode contacts takes place. The redistribution of stimulus amplitudes utilizes re-normalization of amplitudes so that the perceptual level remains fairly constant. This prevents the resulting paresthesia from falling below the perceptual threshold or above the comfort threshold.

Abstract: A small implantable stimulator(s) includes at least two electrodes for delivering electrical stimulation to surrounding tissue. The small stimulator provides means of stimulating a neoplasm with direct electrical current, such as relatively low-level direct current, without the need for external appliances during the stimulation session. The stimulator may be configured to be small enough to be implanted entirely within a neoplasm. Open- and closed-loop systems are disclosed.

Abstract: A small implantable stimulator(s) includes at least two electrodes for delivering electrical stimulation to surrounding tissue. The small stimulator provides means of stimulating the prostate with direct electrical current, such as relatively low-level direct current, without the need for external appliances during the stimulation session. The stimulator may be configured to be small enough to be implanted entirely within the prostate. Open- and closed-loop systems are disclosed.

Abstract: A spinal cord stimulation (SCS) system includes multiple electrodes, multiple, independently programmable, stimulation channels within an implantable pulse generator (IPG) which channels can provide concurrent, but unique stimulation fields, permitting virtual electrodes to be realized. The SCS system includes a replenishable power source (e.g., rechargeable battery), that may be recharged using transcutaneous power transmissions between antenna coil pairs. An external charger unit, having its own rechargeable battery can be used to charge the IPG replenishable power source. A real-time clock can provide an auto-run schedule for daily stimulation. An included bi-directional telemetry link in the system informs the patient or clinician the status of the system, including the state of charge of the IPG battery. Other processing circuitry in the IPG allows electrode impedance measurements to be made. Further circuitry in the external battery charger can provide alignment detection for the coil pairs.

Abstract: A cochlear electrode array is adapted for implantation within the basal end of the scala tympani duct of a human cochlea. A first embodiment of the cochlear electrode array (10) comprises a skinny, elongate carrier (12) of from 6-8 mm in length. Four to eight spaced-apart electrode contacts (14) reside along one of the flat sides of the carrier, each of which is connected to a respective wire (22) embedded within the carrier. The wires exit a proximal end of the carrier via a wire bundle. The wire bundle, in turn, is connectable to an implantable cochlear stimulator (ICS) or equivalent pulse generator. The electrode array (10) is inserted into the relatively straight portion of the basal end of the scala tympani duct of the cochlea through a small slit (42) made in the round window membrane that separates the cochlea from the middle ear. The slit is oriented so as to place the electrode contacts facing the modiolar wall (32).

Abstract: Systems and methods for introducing one or more stimulating drugs and/or applying electrical stimulation to tissue affecting the penis to treat erectile dysfunction (for instance, following prostate surgery) uses at least one implantable system control unit (SCU) producing electrical pulses delivered via electrodes and/or producing drug infusion pulses, wherein the stimulating drug(s) are delivered via one or more pumps and infusion outlets.

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: An improved switching regulator for implantable medical devices includes a control circuit with a capacitor divider to conserve energy, and selectable duty cycles to efficiently match the duty cycle to the charge level in a holding capacitor. The switching regulator charges the holding capacitor to commanded voltage levels, and the holding capacitor provides current for tissue stimulation. The commanded voltage level is reached by “pumping-up” the holding capacitor with the output of the switching regulator. For control purposes, the high voltage (i.e., the voltage across the holding capacitor) is divided between a fixed capacitor and a variable capacitor, and the voltage between the fixed capacitor and the variable capacitor (i.e., the divided voltage) is compared to a reference voltage. The result of the comparison is used to turn-off the switching regulator once the commanded voltage level is reached. The switching duty cycle is set to one of two values.