A superconducting wire comprises a MgB.sub.2 filament, a base material, a high-thermal expansion metal, and a stabilizing material. The high-thermal expansion metal is a metal (for example, stainless steel) having a higher thermal expansion coefficient at room temperature than the MgB.sub.2 and the base material (for example, iron or niobium). The manufacturing method includes a step of packing a mixed powder in a first metal pipe, a step of performing wire-drawing on the first metal pipe formed of the metal to be the base material, a step of producing a composite wire by accommodating the first metal pipe in a second metal pipe formed of the high-thermal expansion metal and the stabilizing material, a step of performing wire-drawing on the composite wire, and a step of performing heat treatment.

A superconducting wire comprises a MgB.sub.2 filament, a base material, a high-thermal expansion metal, and a stabilizing material. The high-thermal expansion metal is a metal (for example, stainless steel) having a higher thermal expansion coefficient at room temperature than the MgB.sub.2 and the base material (for example, iron or niobium). The manufacturing method includes a step of packing a mixed powder in a first metal pipe, a step of performing wire-drawing on the first metal pipe formed of the metal to be the base material, a step of producing a composite wire by accommodating the first metal pipe in a second metal pipe formed of the high-thermal expansion metal and the stabilizing material, a step of performing wire-drawing on the composite wire, and a step of performing heat treatment.

According to one embodiment, a magnetic resonance imaging apparatus includes processing circuitry. The processing circuitry is configured to calculate an allowable amount of heat input to a superconducting magnet, the allowable amount being allocated to each of a plurality of imagings scheduled during a target period. The processing circuitry is configured to determine an imaging condition based on the allowable amount in the each of the plurality of imagings.

According to one embodiment, a magnetic resonance imaging apparatus includes processing circuitry. The processing circuitry is configured to calculate an allowable amount of heat input to a superconducting magnet, the allowable amount being allocated to each of a plurality of imagings scheduled during a target period. The processing circuitry is configured to determine an imaging condition based on the allowable amount in the each of the plurality of imagings.

A magnetic resonance device having a main magnet unit with a cylindrical patient aperture. A gradient connection plate for a gradient coil arrangement surrounds the patient aperture. A cladding arrangement with at least one cladding part outwardly delimits the main magnet unit.

A superconductor bulk magnet magnetizing method providing a more homogenous trapped magnetic field includes: placing the bulk magnet inside a charger bore of an electrical charger magnet; placing a field correction unit inside a superconductor bore of the bulk magnet; applying an electrical current (I.sub.0) to the charger magnet, to generate an externally applied magnetic field, wherein a temperature T.sub.bulk of the bulk magnet exceeds a bulk magnet critical temperature T.sub.c; applying an auxiliary electrical current (I.sub.1, . . . ) to the field correction unit, thus generating an auxiliary magnetic field applied to the bulk magnet from within the superconductor bore, wherein T.sub.bulk>T.sub.c; lowering T.sub.bulk below T.sub.c; turning off the electrical current at the charger magnet, wherein T.sub.bulk<T.sub.c, and turning off the auxiliary electrical current at the field correction unit, wherein T.sub.bulk<T.sub.c; and removing the bulk magnet from the charger bore while T.sub.bulk<T.sub.c.

An electric circuit arrangement for energizing a magnet of a magnetic resonance imaging facility includes a first circuit part, a second circuit part and a control facility. In an embodiment, the first circuit part is designed to generate a direct voltage as an DC link voltage from an alternating voltage and the second circuit part is designed as a current source fed by the DC link voltage. The second circuit part includes a down converter controllable by the control facility, a transformer switchable by the control facility and a rectifier. A primary current is generatable from the DC link voltage via the down converter. The primary current is feedable by a switching facility, switched by the control facility into a primary side of the transformer, and a secondary current for energizing the magnet is generatable via the rectifier connected to a secondary side of the transformer.

An electric circuit arrangement for energizing a magnet of a magnetic resonance imaging facility includes a first circuit part, a second circuit part and a control facility. In an embodiment, the first circuit part is designed to generate a direct voltage as an DC link voltage from an alternating voltage and the second circuit part is designed as a current source fed by the DC link voltage. The second circuit part includes a down converter controllable by the control facility, a transformer switchable by the control facility and a rectifier. A primary current is generatable from the DC link voltage via the down converter. The primary current is feedable by a switching facility, switched by the control facility into a primary side of the transformer, and a secondary current for energizing the magnet is generatable via the rectifier connected to a secondary side of the transformer.

A processing tool for a superconducting magnet of an MRI system is disclosed. The processing tool comprising a first winding part and a second winding part. The first winding part is used as a winding framework for winding a main coil half-body. The second winding part is used as a winding framework for winding a shield coil. The processing tool has an infusion cavity. The infusion cavity comprises a main coil accommodating zone, a shield coil accommodating zone, and a linking zone. The main coil accommodating zone is used for accommodating the main coil half-body wound on the first winding part. The shield coil accommodating zone is used for accommodating the shield coil wound on the second winding part. The main coil accommodating zone is connected to the shield coil accommodating zone via the linking zone. The processing tool helps to reduce the difficulty of superconducting magnet processing.

An assembly of supported superconducting coils may include support structure including a flexible mounting band attached to a surface of a coil and which extends axially beyond the radially outer surface of the coil. The flexible mounting band may be attached to a support structure at multiple locations. The coil may be attached to one or more other coils by the flexible mounting band.