According to some aspects, a low-field magnetic resonance imaging system is provided. The low-field magnetic resonance imaging (MRI) system comprises a magnetics system having a plurality of magnetics components configured to produce magnetic fields for performing MRI, the magnetics system comprising, a B.sub.0 magnet configured to produce a B.sub.0 field for the MRI 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 MRI 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 MRI 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 MRI system.

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.

A coil assembly includes: a radio frequency (RF) coil operable to be placed over a portion of a subject; a quarter-wave transformer coupled to the RF coil and configured to transform a characteristic impedance of the RF coil; and a diode placed behind the quarter-wave transformer and away from the RF coil, wherein the diode is operable to: (i) when the diode is forward biased, the diode turns the quarter-wave transformer into an open circuit such that the power amplifier drives the RF coil with sufficient electrical power for the RF coil to transmit an RF pulse into the portion of the subject; and (ii) when the diode is provided zero or reverse bias, the diode turns the quarter-wave transformer into a short circuit such that the RF coil is detuned from a Lamor frequency of nuclei of interest immersed in the main magnet.

A birdcage coil for a magnetic resonance imaging (MRI) system, the birdcage coil includes: a relatively planar birdcage coil section, including a pair of relatively planar ring portions and a plurality of conductive, elongated rungs extending between the pair of relatively planar ring portions; and a relatively domed birdcage coil section, including a pair of relatively domed ring portions and a plurality of conductive, elongated rungs extending between the pair of relatively domed ring portions. The relatively domed birdcage coil section is releasably coupled to the relatively planar birdcage coil section. In an embodiment, at least two sets of the relatively planar and domed birdcage coil sections are provided, where each of the at least two sets is configured to a different MRI application.

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.

A local coil includes a coil element in the form of a loop. The coil element includes a first conductor, a second conductor, and a third conductor. The coil element includes a first dielectric and a second dielectric. The first dielectric is arranged between the first conductor and the second conductor, and the second dielectric is arranged between the second conductor and the third conductor. The coil element includes a receive unit that includes the first conductor and the second conductor, and a detuning unit that includes the third conductor. In a first operating state of the coil element, the receive unit has a first resonant frequency. In a second operating state of the coil element, the detuning unit is configured to detune the resonant frequency of the receive unit so that the receive unit has a second resonant frequency different than the first resonant frequency.

Various embodiments of the present disclosure are directed towards a magnetic resonance imaging (MRI) radio frequency (RF) coil. The MRI RF coil comprises a first conductive ring and a second conductive ring. A plurality of rung groups extend between the first and second conductive rings. The plurality of rung groups are spaced uniformly about the first conductive ring. Each of the plurality of rung groups comprises a plurality of conductive rungs extending between and connected to the first and second conductive rings. The plurality of conductive rungs of each of the plurality of rung groups are azimuthally separated from one another by a first azimuth angle. Each of the plurality of rung groups is separated from a neighboring rung group by a spacing that forms a window. Each of the windows have a second azimuth angle that is greater than the first azimuth angle.

An MRI antenna array including a housing and a substrate, antenna elements and circuitry encapsulated by the housing. The housing, antenna elements, and substrate are flexible to allow the housing to distort in three dimensions to closely conform to contours of a patient. The antenna elements may be formed from a flat weave mesh conductor. The flat weave mesh conductor allows the MRI antenna array to conform to the contours of a patient to provide three dimensional movement of the array. The flat weave mesh conduct has increased durability over a tight weave mesh of an elongate hollow cylinder conductor, allowing the flat weave mesh conductor to withstand additional flexing cycles.

A radio-frequency (RF) coil for use in a low-field magnetic resonance imaging system and methods of making the same are provided. The RF coil may include a conductor arranged on a substrate in an arrangement such that symmetry in the arrangement cancels at least a portion of a common mode voltage when a current is passed through the conductor. The RF coil may be included in a magnetic resonance imaging (MRI) system for imaging a patient having at least one B.sub.0 magnet for generating a B.sub.0 magnetic field.

According to one embodiment, the MRI apparatus includes an RF coil apparatus having a coil element, a coil port to which the RF coil apparatus is connectible, receive circuitry receiving a signal detected by the RF coil apparatus via the coil port when neither an RF pulse nor a gradient magnetic field is being applied, and performing A/D conversion with an A/D converter, and processing circuitry detecting an abnormality based on the signal. With the RF coil apparatus being connected to the coil port, the receive circuitry switches at least one switch provided in a section between the coil element and the A/D converter between on and off, and receives the signal. The processing circuitry compares a signal of a path where the coil element and A/D converter are connected with a signal of a path where the coil element and A/D converter are not connected, and detects the abnormality.