The present application provides a method of designing a high shielding gradient coil for a planar superconducting magnetic resonance imaging (MRI) system and a gradient coil thereof, the method determines a shielding area according to an outer profile of a metal conductor around the position of the gradient coil in the planar superconducting MRI system, and performs partitioned shielding of a stray field. The constraint values of stray fields at different partitioned zones of the shielding area are adjusted according to the shielding requirements. The primary coils of both the transverse gradient coil and the longitudinal gradient coil optimized by the design method of the high shielding gradient coil contain a reverse coil, which generates a magnetic field that offsets leakage magnetic field of other coils, thus achieving the purpose of reducing the stray field of the gradient coil.

A system for minimizing MGI in a superconducting magnet system of an MRI system includes a thermal shield having bi-metal material. The thermal shield is configured to be disposed about a cold mass of the superconducting magnet system, wherein the bi-metal material is configured to minimize MGI.

A system for minimizing MGI in a superconducting magnet system of an MRI system includes a thermal shield having bi-metal material. The thermal shield is configured to be disposed about a cold mass of the superconducting magnet system, wherein the bi-metal material is configured to minimize MGI.

A superconducting device includes a superconducting cable having a plurality of superconducting tapes in a plurality of phases, including a first phase, and at least one further phase. One or more superconducting tapes of the first phase is in electrical contact with one or more superconducting tapes of the at least one further phase through at least one resistive barrier that prevents current from passing between the first phase and the at least one further phase in the absence of a voltage between one or more of the superconducting tapes of the first phase or the at least one further phase. The first phase is electrically connected in series to at least one further phase.

A superconducting device includes a superconducting cable having a plurality of superconducting tapes in a plurality of phases, including a first phase, and at least one further phase. One or more superconducting tapes of the first phase is in electrical contact with one or more superconducting tapes of the at least one further phase through at least one resistive barrier that prevents current from passing between the first phase and the at least one further phase in the absence of a voltage between one or more of the superconducting tapes of the first phase or the at least one further phase. The first phase is electrically connected in series to at least one further phase.

The invention relates to a device for magnetic measurements and/or magnetic imaging such as an MRI device or a hybrid MEG-MRI device. The device comprises an array of one or more detectors for the magnetic signal and one or more coils for producing preparatory magnetic field pulses. The device further comprises means to drive current pulses through the said coils, wherein at least one of the coils comprises material that is Type-II superconducting at the operating temperature. The device is configured to cancel out at least part of the field generated by the remanent magnetization after a current pulse by the shape of the current pulse and/or the geometrically balanced design of the coil.

The invention relates to a device for magnetic measurements and/or magnetic imaging such as an MRI device or a hybrid MEG-MRI device. The device comprises an array of one or more detectors for the magnetic signal and one or more coils for producing preparatory magnetic field pulses. The device further comprises means to drive current pulses through the said coils, wherein at least one of the coils comprises material that is Type-II superconducting at the operating temperature. The device is configured to cancel out at least part of the field generated by the remanent magnetization after a current pulse by the shape of the current pulse and/or the geometrically balanced design of the coil.

A magnetic resonance imaging (MRI) system includes a superconducting magnet assembly with a superconducting field coil for generating a stationary uniform main magnetic field. A gradient system includes a gradient coil for generating gradient magnetic fields and a gradient amplifier which is connectable to the gradient coil for driving the gradient coil. A switch assembly is adapted for galvanically coupling the superconducting field coil to the gradient amplifier. In this way, it is possible for energizing and discharging a superconducting magnet of an MRI system in an easy and cost-efficient way.

A magnetic resonance imaging (MRI) system includes a superconducting magnet assembly with a superconducting field coil for generating a stationary uniform main magnetic field. A gradient system includes a gradient coil for generating gradient magnetic fields and a gradient amplifier which is connectable to the gradient coil for driving the gradient coil. A switch assembly is adapted for galvanically coupling the superconducting field coil to the gradient amplifier. In this way, it is possible for energizing and discharging a superconducting magnet of an MRI system in an easy and cost-efficient way.

A system comprises a superconducting magnet comprising a coil of superconducting material. The coil includes electrical terminals. The windings of the coil are separated by a metallic conductor. A control circuit is coupled to the terminals to drive a current through the coil to charge the superconducting magnet and configured to provide a current through the coil that is sufficiently small to avoid a quenching effect of the superconducting magnet but also large enough to charge the magnet within a predetermined time period. A cooling structure is thermally coupled to the coil to remove heat caused by charging the superconducting magnet with the current to allow for the current to be sufficiently large to charge the magnet within the predetermined time period without causing the quenching effect.