An implantable pulse generator (IPG) is disclosed having an improved ability to steer anodic and cathodic currents between the IPG's electrodes. Each electrode node has at least one PDAC/NDAC pair to source/sink or sink/source a stimulation current to an associated electrode node. Each PDAC and NDAC receives a current with a magnitude indicative of a total anodic and cathodic current, and data indicative of a percentage of that total that each PDAC and NDAC will produce in the patient's tissue at any given time, which activates a number of branches in each PDAC or NDAC. Each PDAC and NDAC may also receive one or more resolution control signals specifying an increment by which the stimulation current may be adjusted at each electrode. The current received by each PDAC and NDAC is generated by a master DAC, and is preferably distributed to the PDACs and NDACs by distribution circuitry.

Provided is a switched capacitor-based electrical stimulation device which supplies a direct current (DC) power, detects a charging voltage charged in any one of a plurality of capacitors, controls the DC power supplied to a capacitor module to repeat a charging level and a resting level according to a charging pattern when the charging voltage is lower than a target voltage, and outputs an electric current to electrodes which contact a human body based on an output pattern.

Differential charge-balancing can be used in high-frequency neural stimulation. For example, a neural stimulation apparatus can have first and second electrodes configured to be coupled proximate to a nerve fiber to implement a neural stimulation procedure. A neural stimulation circuit can be electrically coupled to the first and second electrodes. The neural stimulation circuit can apply stimulation currents to the nerve fiber through the first and second electrodes during a first stimulation phase of the neural stimulation procedure. The neural stimulation circuit can also apply a modified stimulation current to the nerve fiber through the first electrode during a second stimulation phase of the neural stimulation procedure. The modified stimulation current can be generated based on a difference between (i) a voltage at the first electrode, and (ii) a reference voltage derived from voltages on the first and second electrodes.

In the present invention, an IPG incorporates electrical resistivity monitoring with a reflectometry trigger. The IPG is configured to determine both optically and electrically if migration occurs between the electrodes. If the light intensity variation in the optical trigger is greater than an optical threshold value, then the system will pause stimulation and conduct a resistivity test. A resistivity test is also conducted periodically in the absence of the reflectometry trigger to verify that no lead migration has occurred. The stimulation signal is automatically adjusted if a variation in resistivity values is detected above a resistivity threshold value. The resistivity threshold value is set above the normal variation that occurs due to routine movement of the spinal cord in the spinal canal.

An implantable pulse generator (IPG) including a case containing an energy storage device and one or more electrode leads. A header is coupled to the case. The header includes a cassette, an antenna coupled to the cassette and electrically coupled to the case, the case configured as a part of the antenna for receiving and transmitting electromagnetic signals, and an electrode attachment structure configured to couple with the cassette and configured to couple with the one or more electrode leads.

Implantable medical devices (IMDs) are described. The IMDs are configured to wirelessly receive power from an electromagnetic field provided by an external charger. The IMDs include a conductive case and a header that is typically non-conductive, and which houses a three dimensional antenna structure configured to couple with the external magnetic field. Currents induced in the antenna structure are used to provide power to the IMD. The three dimensional antenna structure may be configured as a cage structure comprising a first loop antenna proximate and parallel to the front of the header, a second loop antenna proximate and parallel to the back of the header, and a third loop antenna proximate and parallel to the top of the header. The three dimensional antenna structure allows the IMD to effectively receive power from different directions, for example, if the orientation of the IMD is flipped or otherwise shifted within the patient's body.

An antenna assembly includes a metal layer configured to emit linearly polarized electromagnetic energy to a receiving antenna implanted underneath a subject's skin; and a feed port configured to connect the antenna assembly to a signal generator such that the antenna assembly receives an input signal from the signal generator and then transmits the input signal to the receiving dipole antenna, wherein the antenna assembly is less than 200 um in thickness, and wherein the metal layer is operable as a dipole antenna with a reflection ratio of at least 6 dB, the reflection ratio corresponding to a ratio of a transmission power of the antenna assembly in transmitting the input signal and a reflection power seen by the antenna assembly resulting from electromagnetic emission of the input signal.

Disclosed herein are systems and methods that can involve a neuromodulation device configured to perform in multiple electrical modulation modes with a single architecture.

An example of a system for delivering neurostimulation may include a programming control circuit and a stimulation control circuit. The programming control circuit may be configured to generate stimulation parameters controlling delivery of the neurostimulation according to a stimulation configuration. The stimulation control circuit may be configured to specify the stimulation configuration, and may include volume definition circuitry and stimulation configuration circuitry. The volume definition circuitry may be configured to determine one or more test volumes, determine a clinical effect resulting from the one or more test volumes each being activated by the neurostimulation, and determine a target volume using the determined clinical effect. The stimulation configuration circuitry may be configured to generate the specified stimulation configuration for activating the target volume.

A voltage regulating module includes a fine regulating charge pump and a voltage-multiplying charge pump. The first output voltage of the fine regulating charge pump is V.sub.1=m*V.sub.0, a second output voltage of the voltage-multiplying charge pump is V.sub.2=n*V.sub.0, and a total output voltage of the voltage regulating module V=V.sub.1+V.sub.2. V.sub.0 is an input voltage, a value of m ranges from 0 to 1, and n is an integer greater than or equal to 1.