According to some aspects, a low-field magnetic resonance imaging system is provided. The low-field magnetic resonance imaging system comprises a magnetics system having a plurality of magnetics components configured to produce magnetic fields for performing magnetic resonance imaging, the magnetics system comprising, a B0 magnet configured to produce a B0 field for the magnetic resonance imaging system at a low-field strength of less than 0.2 Tesla (T), a plurality of gradient coils configured to, when operated, generate magnetic fields to provide spatial encoding of magnetic resonance signals, and at least one radio frequency coil configured to, when operated, transmit radio frequency signals to a field of view of the magnetic resonance imaging system and to respond to magnetic resonance signals emitted from the field of view, a power system comprising one or more power components configured to provide power to the magnetics system to operate the magnetic resonance imaging system to perform image acquisition, and a power connection configured to connect to a single-phase outlet to receive mains electricity and deliver the mains electricity to the power system to provide power needed to operate the magnetic resonance imaging system. According to some aspects, the power system operates the low-field magnetic resonance imaging system using an average of less than 1.6 kilowatts during image acquisition.

Various embodiments of the present disclosure are directed towards a radio frequency (RF) coil comprising a first combination coil and a second combination coil. The first combination coil comprises a first resonant coil and a first resonant shield coupled inductively or by a capacitor, and the first combination coil has a first resonant frequency and a second resonant frequency. The second combination coil comprises a second resonant coil and a second resonant shield coupled inductively or by a capacitor, and the second combination coil has a third resonant frequency and a fourth resonant frequency. The first and second resonant coils are inductively coupled to each other and respectively to the second and first resonant shields. The first and third resonant working frequencies are the same, and the second and fourth resonant isolation frequencies are such that inductive coupling between the first and second resonant coils is negated.

The present disclosure relates to systems and methods for magnetic resonance imaging (MRI). The systems may include a gradient coil assembly configured to form a gradient magnetic field. The systems may also include a cryostat including a superconducting coil assembly and a magnetic field shielding apparatus arranged on/in a component of the cryostat. The superconducting coil assembly may be configured to form a main magnetic field. The magnetic field shielding apparatus may be configured to shield the superconducting coil assembly from a stray field of the gradient coil assembly. The magnetic field shielding apparatus may include a conductive shielding component, a shielding cylinder, or a combination thereof.

According to some aspects, a portable magnetic resonance imaging system is provided, comprising a B.sub.0 magnet configured to produce a B.sub.0 magnetic field for an imaging region of the magnetic resonance imaging system, a noise reduction system configured to detect and suppress at least some electromagnetic noise in an operating environment of the portable magnetic resonance imaging system, and electromagnetic shielding provided to attenuate at least some of the electromagnetic noise in the operating environment of the portable magnetic resonance imaging system, the electromagnetic shielding arranged to shield a fraction of the imaging region of the portable magnetic resonance imaging system. According to some aspects, the electromagnetic shield comprises at least one electromagnetic shield structure adjustably coupled to the housing to provide electromagnetic shielding for the imaging region in an amount that can be varied. According to some aspects, substantially no shielding of the imaging region of the portable magnetic resonance imaging system is provided.

System and methods that reconstruct absolute temperature using a multi-nuclear approach. Specifically, the methods and systems utilize independent NMR/MRI information provided by the precession frequency of two different nuclei to reconstruct a map of the absolute temperature.

The disclosure relates to a gradient coil unit comprising at least one first conductor structure, which is configured to generate a magnetic field gradient in a first direction, and an eddy current compensating conductor structure, which is configured to compensate for a first magnetic field. The first magnetic field is generated by a current induced in the first conductor structure as a result of activation of a conductor structure comprised by the gradient coil unit.

According to some aspects, a low-field magnetic resonance imaging system is provided. The low-field magnetic resonance imaging system comprises a magnetics system having a plurality of magnetics components configured to produce magnetic fields for performing magnetic resonance imaging, the magnetics system comprising, a B.sub.0 magnet configured to produce a B.sub.0 field for the magnetic resonance imaging system at a low-field strength of less than 0.2 Tesla (T), a plurality of gradient coils configured to, when operated, generate magnetic fields to provide spatial encoding of magnetic resonance signals, and at least one radio frequency coil configured to, when operated, transmit radio frequency signals to a field of view of the magnetic resonance imaging system and to respond to magnetic resonance signals emitted from the field of view, a power system comprising one or more power components configured to provide power to the magnetics system to operate the magnetic resonance imaging system to perform image acquisition, and a power connection configured to connect to a single-phase outlet to receive mains electricity and deliver the mains electricity to the power system to provide power needed to operate the magnetic resonance imaging system. According to some aspects, the power system operates the low-field magnetic resonance imaging system using an average of less than 1.6 kilowatts during image acquisition.

A particle therapy system includes an accelerator 1 which generates a particle beam for extraction, an irradiation apparatus 21 which irradiates the particle beam to an irradiation target 26, a gantry 18 which rotates together with the irradiation apparatus 21, and an MRI apparatus 50 which rotates together with the gantry 18. The MRI apparatus 50 includes a magnetic circuit composed of an iron core 60 and a plurality of coils 61 serving as a magnetic flux source. The iron core 60 includes two oppositely disposed magnetic poles 63A and 63B, and a return yoke 64 for connecting the magnetic poles 63A and 63B. The magnetic poles 63A, 63B have cavities 65A, 65B. The particle beam passing through the cavity 65A is irradiated to the irradiation target 26.

Gradient coil assemblies for horizontal magnetic resonance imaging systems (MRIs) and methods of their manufacture. Some embodiments may be used with open MRIs and can be used with an instrument placed in the gap of the MRI. In general, concentrations of conductors or radially oriented conductors may be moved away from the gap of the MRI so as to reduce eddy currents that may be induced in any instrument placed within the gap. Systems for directly cooling primary gradient and shield coils may be utilized and various coil supporting structures may be used to assist in coil alignment or to facilitate use of an instrument in the MRI gap.

The invention relates to a gradient shield coil (5) for a MRI apparatus (1). The gradient shield coil (5) according to the invention comprises windings (6, 7) around its longitudinal axis (A), wherein at least one winding (7) is arranged as a meandering winding (7). This meandering winding (7) comprises multiple contiguous sections (8) along its circumference, wherein in each of these sections (8) a pair of conductor loops (9, 10) is provided in such a way that a current in the meandering winding (7) would run in opposite directions in the two conductor loops (9, 10). In this way, dissipation in the superconductive coils of a superconductive magnet (2) of a respective MRI apparatus (1) may be further reduced.