A method of monitoring depletion of a coolant in a cooling system associated with imaging modality is disclosed. The method includes receiving set of signal values from sensing unit, wherein set of signal values correspond to parameters of cooling system, determining class associated with set of signal values using an artificial intelligence model, selecting prediction model capable of predicting depletion rate of the coolant based on class associated with set of signal values, computing depletion rate of coolant in cooling system based on set of signal values using the selected prediction model, determining number of days remaining to refill the coolant in cooling system based on the depletion rate of the coolant in cooling system, and generating warning signal on graphical user interface, warning signal indicative of number of days remaining to refill coolant in cooling system.

The present disclosure relates to using an integrated cooling circuit to provide both forced-flow pre-cooling functionality and closed-loop thermosiphon cooling for persistent mode operation of a superconducting magnet. In one embodiment, the integrated cooling circuit shares a single set of cooling tubes for use with both the forced-flow pre-cooling circuit as well as the closed-loop operating-state cooling circuit.

Apparatus for imaging during surgical procedures includes an operating room for the surgical procedure and an MRI for obtaining images periodically through the surgical procedure by moving the magnet up to the table. The magnet wire is formed of a superconducting material such as magnesium di-boride or Niobium-Titanium which is cooled by a vacuum cryocooling system to superconductivity without use of liquid helium. The magnet weighs less than 1 to 2 tonne and has a floor area in the range 15 to 35 sq feet so that it can be carried on the floor by a support system having an air cushion covering the base area of the magnet having side skirts so as to spread the weight over the entire base area. The magnet remains in the room during surgery and is powered off to turn off the magnetic field when in the second position remote from the table.

A coil for single-sided magnetic resonance imaging system is disclosed. The coil is configured to generate a magnetic field outwards away from the coil. The coil includes a first ring and a second ring having different diameters and the current flows through the coil to generate the magnetic field in a region of interest. A method of imaging via a magnetic imaging apparatus is also disclosed. The method includes providing a power source and providing a coil that includes a first ring and a second ring having different diameters. The method includes turning on the power source so as to flow a current through the coil to generate a magnetic field in a region of interest. The method also includes selectively turning on a particular set of electronic components so as to pulse the magnetic field in a narrower frequency range.

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.

A conduction-cooled radiofrequency coil subsystem of MRI system with high signal-to-noise ratio imaging capability at low field and/or ultra-low field. The conduction-cooled RF coil subsystem includes a radiofrequency (RF) coil module having at least one RF instrumentation; a cryocooler; and a thermal conduction line thermally connected between the cryocooler and the RF instrumentation. The RF coil module further includes a housing defining a thermally insulated vessel for accommodating the RF instrumentation. The thermal conduction line is thermally coupled to the cryocooler which is located outside the housing of the RF coil module and the RF instrumentation in the thermally insulated vessel to conduction cool the RF instrumentation. The at least one RF instrumentation includes one or more of an RF transceiver coil, an RF receiver coil, an RF preamplifier and an RF electronics module.

A magnetic field generator includes a refrigerating machine, a cold head, a superconductor which is formed in a cylindrical shape, a cold head extension portion which extends from the cold head and is brought into thermal contact with the superconductor at its extended end; and a vacuum heat insulating container having an internal space in which the cold head, the cold head extension portion, and the superconductor are received. The superconductor has a room temperature bore space, which is formed on its inner peripheral side along an axial direction of the superconductor, and is spatially isolated from the internal space of the vacuum heat insulating container. The room temperature bore space has both ends communicating to an outside of the magnetic field generator.

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 conduction-cooled radiofrequency coil subsystem of MRI system with high signal-to-noise ratio imaging capability at low field and/or ultra-low field. The conduction-cooled RF coil subsystem includes a radiofrequency (RF) coil module having at least one RF instrumentation; a cryocooler; and a thermal conduction line thermally connected between the cryocooler and the RF instrumentation. The RF coil module further includes a housing defining a thermally insulated vessel for accommodating the RF instrumentation. The thermal conduction line is thermally coupled to the cryocooler which is located outside the housing of the RF coil module and the RF instrumentation in the thermally insulated vessel to conduction cool the RF instrumentation. The at least one RF instrumentation includes one or more of an RF transceiver coil, an RF receiver coil, an RF preamplifier and an RF electronics module.

A system may comprise a magnetic resonance imaging (MRI) device including a bore that is configured to accommodate a subject. The MRI device may include multiple superconducting magnets configured to generate a magnetic field in the bore. The MRI device may include one or more superconducting connections each of which is configured to connect at least two of the multiple superconducting magnets. The system may further include a radiation source configured to emit a radiation beam toward the bore. The radiation source may be able to rotate in a plane perpendicular to a direction of the magnetic field in the bore. The MRI device may further include one or more protection components configured to prevent at least a portion of the radiation beam from irradiating the one or more superconducting connections.