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.

A radio frequency transmit system (40) for use in magnetic resonance imaging apparatuses, comprising a radio frequency driver unit (42) including at least a first radio frequency power source (44; 82) and a second radio frequency power source (46; 84), a radio frequency coil arrangement (48) for generating an RF magnetic excitation field B.sub.1, and a plurality of switching members (68, 70, 72, 74) electrically connecting the radio frequency power sources (44, 46; 82, 84) to different pairs of drive ports (58, 60, 62, 64) in a first and in at least a second switching status. The first drive port (58) of the first pair of drive ports (58, 60) and the first drive port (62) of the at least second pair of drive ports (62, 64) are arranged spaced by a fixed predetermined angular distance in the azimuthal direction (56) about the center axis (50); and a magnetic resonance imaging system (10) including such radio frequency transmit system (40).

A TEM resonator system includes at least two TEM resonators, especially in the form of TEM volume coils, and especially for use in an MR imaging system or apparatus for transmitting RF excitation signals and/or for receiving MR signals into/from an examination object or a part thereof, respectively. The TEM resonators are arranged and displaced along a common longitudinal axis, and an intermediate RF shield is positioned in longitudinal direction between the two TEM resonators for at least substantially preventing electromagnetic radiation from emanating from between the first TEM resonator and the second TEM resonator into the surroundings.

A MRI system includes a RF coil assembly, a gradient coil assembly disposed around the RF coil assembly, the gradient coil assembly including a RF shield, and a superconducting magnet assembly disposed around the gradient coil assembly, the superconducting magnet assembly including a vessel containing a plurality of superconducting coils. The RF coil assembly includes a plurality of RF coil elements applied on an outer surface of a hollow cylindrical RF coil former. The plurality of RF coil elements includes a plurality of rungs and a plurality of ground patches that are connected. The plurality of ground patches are spaced apart from the RF shield with a dielectric material in between, and the plurality of ground patches are capacitively coupled to the RF shield. The RF coil assembly is a TEM RF body coil.

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.

In order to provide a technique in which, in the TEM type antenna, the uniformity of sensitivity in the internal portion of the antenna can be maintained with simple configuration, without scarifying the internal space of the antenna, regardless of a size, a shape and a location of a load, and also regardless of locations of the constitutional members of the antenna, the TEM type antenna includes rung conductors which branch out into plural pieces in the middle portion and join into one piece in the two end portions. In other words, the rung conductor having a void space in the middle portion of the rung conductor in the longitudinal direction is provided. The adjacent rung conductors are disposed to be further closer to each other in the middle portion, and to maintain the same distance as that in the related art in the end portion.

In one embodiment, a magnetic resonance apparatus includes a gradient coil configured to be cylindrically-shaped and to apply a gradient magnetic field to a hollow region into which an object is inserted, the hollow region being formed, the hollow region being formed inside the gradient coil; and an RF coil configured to include a resonance circuit whose plural connecting conductors are folded back at one end side of the gradient coil so that the resonance circuit extends from the hollow region to an outer region of the gradient coil.

Provided is an antenna such as a TEM-type antenna and a microstrip-type antenna that has rung conductors and a shield conductor to electrically connect and use them. A holding member that maintains a shape of the shield conductor is composed by assembling ribs and thin walls. An inner holding member is a structural material. Holes are provided on at least either one of the shield conductor and the holding member adhered thereto or the inner holding member, which can adjoin conductors from the outside of the cylindrical antenna through the said holes during the antenna production.

A radio frequency (RF) antenna device (140) applies an RF field to an examination space (116) of a magnetic resonance (MR) imaging system (110). The RF antenna device (140) has a tubular body and is segmented in its longitudinal direction (154). Each segment (162, 164) has at least one activation port. The result is that each mode, corresponding to an activation port, may be controlled individually. Accordingly, the inhomogeneity of the subject of interest in the longitudinal direction of the RF antenna device can directly be addressed. There are different ways to build up a z-segmented RF antenna device.

A progressive series of five new coils is described. The first coil solves problems of transmit-field inefficiency and inhomogeneity for heart and body imaging, with a close-fitting, 16-channel TEM conformal array design with efficient shield-capacitance decoupling. The second coil progresses directly from the first with automatic tuning and matching, an innovation of huge importance for multi-channel transmit coils. The third coil combines the second, auto-tuned multi-channel transmitter with a 32-channel receiver for best transmit-efficiency, control, receive-sensitivity and parallel-imaging performance. The final two coils extend the innovative technology of the first three coils to multi-nuclear (.sup.31P.sup.1H) designs to make practical human-cardiac imaging and spectroscopy possible for the first time at 7 T.