Example neurostimulation induced medicine devices and methods of use are described herein. An example endotracheal device can include an elongate tubular member having a proximal end and a distal end, an inflatable cuff arranged between the proximal and distal ends of the elongate tubular member, and an electrode array disposed in proximity to an exterior surface of the inflatable cuff. The inflatable cuff can be configured to expand to contact a subject's tracheal wall. Additionally, the electrode array can include a plurality of flexible electrodes, where a set of the flexible electrodes anatomically align with a region of the subject's tracheal wall for selectively targeting vagus nerve activity.

A filtered feedthrough assembly includes a ferrule configured to be installed in an AIMD housing. An insulator is disposed within a ferrule opening. A conductive pathway is disposed within a passageway through the insulator. A filter capacitor is disposed on a device side having active and ground electrode plates disposed within a capacitor dielectric k greater than 0 and less than 1,000. A capacitor active metallization is electrically connected to the active electrode plates. A ground capacitor metallization is electrically connected to the ground electrode plates. The filter capacitor is the first filter capacitor electrically connected to the conductive pathway coming from a body fluid side into the device side. An active electrical connection electrically connects the conductive pathway to the capacitor active metallization. A ground electrical connection electrically connects the ground capacitor metallization to the ferrule. The filter capacitor is a flat-through or an X2Y attenuator filter capacitor.

A particle alignment method in accordance with at least one of the present inventions includes the step of positioning a cochlear implant, which is implanted within a patient's head and which includes a magnet apparatus with a central axis and magnetic material particles, at a location outside of the scanning area of an MRI system, adjacent to the MRI system, and within the MRI magnetic field in such a manner that the central axis of the magnet apparatus is at least substantially parallel to the MRI magnetic field.

A system for validating safety of a medical device in a presence of a magnetic resonance imaging (MRI) field is provided. The system includes a first electric field generating device configured to form first electric field and configured to receive a medical device at least partially within the first electric field, and a second electric field generating device configured to form a second electric field in proximity to the first electric field and configured to receive the medical device at least partially within the second electric field. One or more processors are configured to execute program instructions to calculate predicted parameter values of the medical device based on a transfer function, the transfer function defined to predict a safety characteristic of the medical device when in the presence of an MRI field, obtain measured parameter values from the medical device, the measured parameter values indicative of the safety characteristic of the medical device when exposed to the first and second electric fields, and compare the measured parameter values to the predicted parameter values in connection with validating the transfer function.

An electrode system includes an electrode, a connector, and a cable with an in- line radio-frequency filter module comprising resistors and inductors without any deliberately added capacitance. The resistors are arranged in an alternating series of resistors and inductors, preferably with resistors at both outer ends, and connected electrically in series. The in-line module is located at a specific location along the wire, chosen through computer modeling and real-world testing for minimum transfer of received RF energy to a patient's skin, such as between 100 cm and 150 cm from the electrode end of a 240 centimeter cable. The total resistance of the resistors plus cable, connectors and solder is 1000 ohms or less; while the total inductance is roughly 1560 nanohenries. The inductors do not include ferrite or other magnetic material and are, together with the resistors, stock components thereby simplifying manufacture and reducing cost.

In some examples, an implantable medical device (IMD) includes a stimulation generator and/or sensing circuitry configured to generate electrical stimulation for delivery to or sensing the state of a patient via electrode coupled to the IMD; interconnect circuitry configured to transport the electrical stimulation from the stimulation generator to the lead, the interconnect circuitry comprising: a feedthrough capacitor; and one or more components and a switch that are collectively electrically connected in parallel with the feedthrough capacitor; and processing circuitry configured to selectively close the switch based on a magnetic resonance imaging (MRI) status of the IMD.

Systems and methods are disclosed for use with Implantable Medical Devices (IMD) such as Implantable Stimulator Devices. The system includes a permanent magnet which can be used to reset the IMD (such as during an emergency) and to place the IMD in a pairing mode to establish communications with an external device. An external device paired to the IMD can be used to place the IMD in an MRI mode that renders the IMD safe during a Magnetic Resonance Imaging (MRI) scan. In the event that the external device is unavailable to cause the IMD to exit the MRI mode, the bar magnet can also be used in the MRI mode to pair the IMD with another external device.

A system and/or method involving sensing first data via at least one implantable sensor of an implantable medical device (IMD) system, and identifying a presence-absence state of a magnetic resonance imaging (MRI) system using the first data.

An apparatus, including an implantable portion of a hearing prosthesis, wherein the apparatus is configured to at least partially cancel a signal in the implantable portion, the signal resulting from an external magnetic field generated external to a recipient of the hearing prosthesis. In an exemplary embodiment, the signal is a signal generated by the external magnetic field interacting with an electrical lead extending between a stimulation output device of the prosthesis and a stimulator and/or receiver of the implantable portion.

Embodiments of the present invention are directed to an implantable hearing implant, such as cochlear implants. The implantable hearing implant includes an implant device containing signal processing circuitry configured to receive an implant communications signal transmitted from an external transmitting coil. The implantable hearing implant further includes an implant magnet configured to cooperate with a corresponding external holding magnet in an external device located over the overlying skin to magnetically hold the external device against the overlying skin. The implant magnet has a north magnetic pole, a south magnetic pole, and as a whole has an overall magnetic dipole moment that is parallel to or at an angle of 300 or less with respect to the outermost surface. The implant magnet has a north end portion and a south end portion, each having an individual magnetic dipole moment that is inclined with respect to the overall magnetic dipole moment.