Systems, methods and devices are configured for integrated parallel reception, excitation, and shimming (iPRES). Parallel transmit/receive (which can include B.sub.1 shimming and/or parallel imaging capabilities) and B.sub.0 shimming employ the same set of localized coils or transverse electromagnetic (TEM) coil elements, with each coil or TEM element working in both an RF mode (for transmit/receive and B.sub.1 shimming) and a direct current (DC) mode (for B.sub.0 shimming) simultaneously. Both an RF and a DC current can flow in the same coil simultaneously but independently with no electromagnetic interference between the two modes. This invention is not only applicable when the same coil array is used for parallel transmit, receive and shim, but also when two separate coil arrays are used. In that case, the B.sub.0 shimming capability can be integrated into one of the coil arrays (i.e. a transmit array with B.sub.1 shimming capability or a receive array), thereby increasing the flexibility and practical utility of the iPRES technology.

A RF conductive member for a magnetic resonance imaging (MRI) resonator includes an opening, a butterfly pickup loop, and a sensor cable. The RF conductive member has a length, a width, and a depth, and is configured to conduct a RF conductive member current. The opening passes through the depth of the RF conductive member and is disposed along the length of the RF conductive member. The butterfly pickup loop is disposed within the opening and configured to detect the RF conductive member current. The butterfly pickup loop includes a first loop and a second loop. The second loop is proximate the first loop and co-planar with the first loop. The sensor cable extends from the butterfly pickup loop and is configured to communicably couple the butterfly pickup loop with at least one processing unit.

Systems, methods and devices are configured for integrated parallel reception, excitation, and shimming (iPRES). Parallel transmit/receive (which can include B?1#191 shimming and/or parallel imaging capabilities) and B.sub.1 shimming employ the same set of localized coils or transverse electromagnetic (TEM) coil elements, with each coil or TEM element working in both an RF mode (for transmit/receive and B.sub.1 shimming) and a direct current (DC) mode (for B.sub.0 shimming) simultaneously. Both an RF and a DC current can flow in the same coil simultaneously but independently with no electromagnetic interference between the two modes. This invention is not only applicable when the same coil array is used for parallel transmit, receive and shim, but also when two separate coil arrays are used. In that case, the B.sub.0 shimming capability can be integrated into one of the coil arrays (i.e. a transmit array with B.sub.1 shimming capability or a receive array), thereby increasing the flexibility and practical utility of the iPRES technology.

MRI systems with a new concept and hardware modality configured for parallel transmit, receive, and shim to address B.sub.0 and B.sub.1 inhomogeneity, both of which increase with field strength. This invention benefits from a number of advantages over existing technologies: it can save valuable space within the MRI magnet bore, largely reduce the manufacturing cost of MRI scanners, and avoid the electromagnetic interference issue associated with existing technologies.

A phased array radio-frequency (RF) coil includes a cylindrical frame including a coaxial inner frame and a coaxial outer frame having different diameters; and vertical loop coils arranged in a circumferential direction of the cylindrical frame. Each vertical loop coil includes an inner conductor extending in a lengthwise direction on the coaxial inner frame; an outer conductor extending in a lengthwise direction on the coaxial outer frame and facing the inner conductor; and a first resonant frequency adjustment capacitor for connecting one end of the inner conductor in the lengthwise direction and one end of the outer conductor in the lengthwise direction so that the phased array RF coil resonates at an MR operating frequency.

A magnetic resonance imaging (MRI) system comprises, a main magnet, a gradient coil and an RF coil. The main magnet generates a static magnetic field, the gradient coil which is formed inside the main magnet and generates a gradient magnetic field and the RF coil. The RF coil is formed inside the gradient coil and comprises a plurality of different components including: a former supporting the plurality of different components including windings and having a first area and a second area and a groove formed in the second area and in which a component of the RF coil is installed and inset, reducing thickness of the RF coil.

In order to provide a technique which can suppress coupling to homogenize the spatial distribution of an RF magnetic field and can improve penetration of the RF magnetic field into the subject, pad-like electric field conductors having a predetermined area are provided outside both ends of a rung conductor as a part of a configuration which forms a loop-like circuit and is driven as an antenna. An antenna device includes a sheet-like conductor, a rung conductor which is arranged at a predetermined distance from the sheet-like conductor, two electric field conductors which are arranged in both end portions of the rung conductor at a predetermined distance from the sheet-like conductor, and connection terminals which are transmission and reception terminals provided in the rung conductor and the sheet-like conductor. The rung conductor and the sheet-like conductor configure a loop circuit which resonates at a preset frequency.

A technique is provided to reserve large examination space in the tunnel type MRI apparatus, without increasing production cost nor reducing significantly irradiation efficiency and homogeneity in an irradiation distribution within an imaging region. The present invention provides an RF coil unit in which four partial cylindrical coils are placed with a gap therebetween in the circumferential direction inside a cylindrical RF shield, in such a manner that two pairs of the partial cylindrical coils are opposed to each other, and magnetic fields produced by the individual partial cylindrical coils are combined, thereby producing a circularly polarized wave field or an elliptically polarized wave field. The partial cylindrical coil is provided with a partial cylindrical conductor, multiple first conductors substantially parallel with the central axis of the RF shield, multiple capacitors connecting both ends of the first conductors with the partial cylindrical conductor, and a second conductor adjacent to at least one of the ends of the first conductor. The partial cylindrical coils are respectively provided with high frequency signals having a desired amplitude ratio and phase difference, while a reference frequency thereof being identical.

a radio frequency (RF) coil device includes a plurality of RF coil elements configured to generate an RF magnetic field, and a support member configured to support the plurality of RF coil elements so that at least one of the plurality of RF coil elements is movable.

The embodiments relate to a body coil, to a magnetic resonance device, and to a method for operating a magnetic resonance device. The body coil includes at least one antenna unit and at least one pre-amplification unit, wherein the pre-amplification unit is arranged at a feed point of the antenna unit, wherein the pre-amplification unit has an input reflection factor at the feed point of the antenna unit whose value is greater than 0.7.