Abstract:
A charging system for an Implantable Medical Device (IMD) is disclosed having a charging coil and one or more sense coils. The charging coil and one or more sense coils are preferably housed in a charging coil assembly coupled to an electronics module by a cable. The charging coil is preferably a wire winding, while the one or more sense coils are concentric with the charging coil and preferably formed in one or more traces of a circuit board. The magnitude of one or more voltages induced on the one or more sense coils can be measured to determine the position of the charging coil relative to the IMD, and in particular whether the charging coil is (i) centered, (ii) not centered but not misaligned, or (iii) misaligned, with respect to the IMD being charged, which three conditions sequentially comprise lower coupling between the charging coil and the IMD.
Abstract:
A charging system for an Implantable Medical Device (IMD) is disclosed having a charging coil and one or more sense coils. The charging coil and one or more sense coils are preferably housed in a charging coil assembly coupled to an electronics module by a cable. The charging coil is preferably a wire winding, while the one or more sense coils are concentric with the charging coil and preferably formed in one or more traces of a circuit board. The magnitude of one or more voltages induced on the one or more sense coils can be measured to determine the position of the charging coil relative to the IMD, and in particular whether the charging coil is (i) centered, (ii) not centered but not misaligned, or (iii) misaligned, with respect to the IMD being charged, which three conditions sequentially comprise lower coupling between the charging coil and the IMD.
Abstract:
Receiver and demodulation circuitry for an external controller for an implantable medical device is disclosed. The circuitry comprises two high Quality-factor band pass filters (BFPs) connected in series. Each BFP is tuned to a different center frequency, such that these center frequencies are outside the band of frequencies transmitted form the IMD. The resulting frequency response is suitably wide to receive the band without attenuation, but sharply rejects noise outside of the band. The resulting filtered signal is input to a comparator to produce a square wave of the filtered signal, which maintains the frequencies of the received signal and is suitable for input to a digital input of a microcontroller in the external controller. Demodulation of the square wave occurs in the microcontroller, and involves assessing the time between transitions in the square wave. These transmission timings are compared to expected transition times for the logic states in the transmitted data. The results of these comparisons are stored and filtered to remove noise and to recover the transmitted data.
Abstract:
A charging system for an Implantable Medical Device (IMD) is disclosed having a charging coil and one or more sense coils. The charging coil and one or more sense coils are preferably housed in a charging coil assembly coupled to an electronics module by a cable. The charging coil is preferably a wire winding, while the one or more sense coils are concentric with the charging coil and preferably formed in one or more traces of a circuit board. One or more voltages induced on the one or more sense coils can be used to determine whether the charging coil is (i) centered, (ii) not centered but not misaligned, or (iii) misaligned, with respect to the IMD being charged, which three conditions sequentially comprise lower coupling between the charging coil and the IMD. A charging algorithm is also disclosed that control charging dependent on these conditions.
Abstract:
Receiver and digital demodulation circuitry for an external controller for communicating with an implantable medical device (IMD) is disclosed. A Digital Signal Processor (DSP) is used to sample received analog data transmitted from the IMD at a lower rate than would otherwise be required for the frequency components in the transmitted data by the Nyquist sampling criteria. To allow for this reduced sampling rate, the incoming data is shifted to a lower intermediate frequency using a switching circuit. The switching circuit receives a clock signal, which is preferably but not necessarily the same clock signal used by the DSP to sample the data. The switching circuit multiplies the received data with the clock signal to produce lower intermediate frequencies, which can then be adequately sampled at the DSP at the reduced sampling rate per the Nyquist sampling criteria.
Abstract:
A charging system for an Implantable Medical Device (IMD) is disclosed having a charging coil and one or more sense coils preferably housed in a charging coil assembly coupled to an electronics module by a cable. The charging coil is preferably a wire winding, while the sense coils are preferably formed in one or more traces of a circuit board. One or more voltages induced on the one or more sense coils can be used to determine one or more parameters (magnitude, phase angle, resonant frequency) indicative of the position between the charging coil and the IMD, which position may include the radial offset and possibly also the depth of the charging coil relative to the IMD. Knowing the position, the power of the magnetic field produced by the charging coil can be adjusted to compensate for the position.
Abstract:
A charging system for an Implantable Medical Device (IMD) is disclosed having a charging coil and one or more sense coils. The charging coil and one or more sense coils are preferably housed in a charging coil assembly coupled to an electronics module by a cable. The charging coil is preferably a wire winding, while the one or more sense coils are concentric with the charging coil and preferably formed in one or more traces of a circuit board. One or more voltages induced on the one or more sense coils can be used to determine the resonant frequency of the charging coil/IMD coupled system. The determined resonant frequency can then be used to determine the position of the charging coil relative to the IMD. The magnetic field produced from the charging coil may also be driven at the resonant frequency to optimize power transfer to the IMD.
Abstract:
A neurostimulation device and system are provided. At least one neurostimulation lead having a plurality of electrodes is configured for being implanted within tissue of a patient. A shunt capacitance is coupled to one of the electrodes. Time-varying electrical current is delivered to at least one of the electrodes, wherein the shunt capacitance would, without compensation, absorb charge from or inject charge into the tissue in response to time-varying changes in the delivered electrical current, thereby causing an uncompensated electrical waveform to be delivered to the tissue adjacent the one electrode, The absorbed or injected charge is at least partially compensated for, thereby causing a compensated electrical waveform to be delivered to the tissue adjacent the one electrode.
Abstract:
A charging system for an Implantable Medical Device (IMD) is disclosed having a charging coil and one or more sense coils preferably housed in a charging coil assembly coupled to an electronics module by a cable. The charging coil is preferably a wire winding, while the sense coils are preferably formed in one or more traces of a circuit board. One or more voltages induced on the one or more sense coils can be used to determine a phase angle between the voltage and a driving signal for the charging coil. The determined phase angle can then be used to determine the position of the charging coil relative to the IMD. Additionally, more than one parameter (phase angle, magnitude, resonant frequency) may be determined using the voltage may be used to determine position, including the radial offset and depth of the charging coil relative to the IMD.
Abstract:
A charging system for an Implantable Medical Device (IMD) includes a split charging coil for generating a magnetic field to provide power to the IMD. The split charging coil includes a first coil portion and a second coil portion, each of which can be formed as a mechanical winding of an insulated conductor. The first and second coil portions are connected to each other in a way that substantially reduces or eliminates any current-carrying path that is routed radially with respect to the coil. As a result, the split coil produces a uniform magnetic field that enables a more accurate determination of alignment between the coil and the IMD than is available using traditional charging coils.