A cooling channel in a gantry of a medical imaging apparatus transfers heat away from the radiation detector and detector electronics, while limiting influence on magnetic fields generated within the gantry, when incorporated in a magnetic resonance imaging (MRI) system. The cooling channel includes a non-electrically conducting, non-metallic housing in conductive thermal communication with the detector electronics and the radiation detector. A cooling conduit in the housing circulates coolant fluid. A unitary, non-electrically conductive, non-metallic heat sink in the housing is in direct conductive, thermal communication with the housing and the cooling conduit. A solid, thermally conductive layer is interposed between and affixed to opposing, spaced exterior surfaces of the conduit and the heat sink

According to one embodiment, a magnetic resonance imaging system includes a first imaging apparatus, a first cooling system, a second imaging apparatus, a second cooling system and a cooling control device. The first imaging apparatus includes a first magnet configured to generate a static magnetic field. The first cooling system is configured to cool the first magnet. The second imaging apparatus includes a second magnet configured to generate a static magnetic field. The second cooling system is configured to cool the second magnet. The cooling control device is configured to switch a cooling target of each of the first cooling system and the second cooling system.

The present disclosure may provide a magnetic resonance (MR) system. The MR system may include a magnet assembly, a gradient coil assembly, and a shim assembly. The magnet assembly may be configured to generate a main magnetic field. The magnet assembly may include a magnet and a cryostat configured to cool the magnet located inside the cryostat. The cryostat may form a bore. The gradient coil assembly may be configured to generate a gradient magnetic field. The gradient coil assembly may be located inside the bore. The shim assembly may be configured to at least partially shield a stray field which is generated by the gradient coil assembly and to which the magnet is subjected. The shim assembly may be located outside the gradient coil assembly.

At least one example embodiment provides a magnetic resonance imaging system comprising at least one local radiofrequency (RF) coil; and at least one marker element, wherein the magnetic resonance imaging system is configured to activate the at least one marker element and deactivate the at least one marker element such that the at least one marker element is detectable by the magnetic resonance imaging system at a position relative to the at least one local RF coil if the at least one marker element is activated, and the at least one marker element is not detectable by the magnetic resonance imaging system if the at least one marker element is deactivated.

An upper coil assembly for use with a lower RF coil assembly mounted to provide an RF probe arranged to be engaged with a head of a patient in MRI includes a plurality of coil loops arranged in a row defining a phase shift coil array with each coil loop including an independent output conductor for communicating signals to a respective preamplifier for independent amplification and each coil loop including a plurality of capacitors at spaced positions therearound. To decouple the loops each coil loop partly overlaps a next coil loop with a first decoupling capacitor shared on a common portion of each coil loop and each next coil loop. The first and third coil loops are also decoupled by using third decoupling capacitor in a connecting conductor between the first and third coil loops.

An NMR magnet system uses a Stirling cooler having a cold head that extends into a housing of the system to cool a cold shield surrounding a cryogen vessel. The system may have a damper located between the cooler and the cold shield to reduce a transmission of vibration from the cooler to a magnet coil immersed in the cryogen. The damper may be passive, or may be part of an active damping system that uses an acceleration sensor to drive an active damper that compensates for cooler vibration. A compensation apparatus may use a stored characteristic of a signal distortion caused by the vibration and, in response to a trigger signal from the cooler, apply compensation to an excitation signal provided to a sample by an NMR probe in a bore of the magnet coil, or to an FID signal from the sample that is detected by the probe.

A system for medical data acquisition comprising a plurality of scanners and a plurality of infrastructure units to operate the scanners, wherein the system is designed to use at least one of the infrastructure units as a common infrastructure unit to operate at least two of the scanners. Also, a method to control this system.

A cooling system of a magnetic resonance apparatus is disclosed. In the cooling system, a first cooling device and a second cooling device are used to realize a secondary step of cooling of a circulating fluid without energy consumption, thereby reducing the operating energy consumption of the cooling system. In addition, a magnetic resonance apparatus comprising the cooling system is further provided.

A pair of detection coils, one coil provided on each side of a sample container across the width of the sample container. The detection coil is made of a superconductor and has an electric circuit pattern capable of detecting a magnetic resonance signal from a sample. The detection coil includes a lateral component intersectional to a static magnetic field H.sub.0 and having a part disposed at a position spaced away from a detection region, as compared to the remaining part.

A method and apparatus for receiving (RX) radio-frequency (RF) signals suitable for MRI and/or MRS from a plurality of MRI “coil elements” (antennae), each contained in one or a plurality of body-coil parts, wherein the body-coil parts are easily assemble-able into a body-coil assembly (e.g., in some embodiments, a cylindrical body-coil assembly) with shield elements that are overlapped and/or concentric, and wherein the body-coil assembly is readily disassemble-able for easier shipping, and wherein the body-coil parts are optionally usable individually as transmit (TX) and/or receive (RX) coil elements for MRI. In some embodiments, the system provides for repeatable assembly and disassembly for ease of maintenance (such as frequency tuning and impedance matching) such that the body-coil assembly can be fully assembled and tested, then taken apart for less costly and easier shipping (with reduced risk of damage) and then reassembled at the destination for operation in an MRI system.