Disclosed is a single-sided magnetic imaging apparatus, comprising a permanent magnet, wherein a Z axis is defined through the permanent magnetic into a field of view. The single-sided magnetic imaging apparatus further comprises an electromagnet, a gradient coil set, a radio frequency transmission coil, a radio frequency reception coil, and a power source. The power source is configured to generate an electromagnetic field in the field of view along the Z axis. The electromagnetic field comprises a field gradient in the field of view, wherein a timing of the radio frequency transmission coil is configured to target a location within the field gradient in the field of view.

For a receiving surface coil (1) for detecting nuclear magnetic resonance signals from a patient a solution for an easy adaption of the receiving surface coil (1) to the anatomy of the patient shall be created. This is achieved by a receiving surface coil (1) for detecting nuclear magnetic resonance signals from a patient, the receiving surface coil (1) comprising: a flexible housing (13) with an opening (2), a set of RF loop elements (8, 9) housed in the flexible housing (13), wherein the set of RF loop elements (8, 9) comprises at least a central loop (9) element running around the opening (2) in the flexible housing (13) and a plurality of loop elements (8) arranged around the opening (2).

Provided is a quad-core radio-frequency coil circuit. The quad-core radio-frequency coil circuit includes a coil module (1) and a front-end module (2). The coil module (1) is configured to receive a nuclear magnetic test signal and, according to the nuclear magnetic test signal, generate an induction signal. The front-end module (2) is connected to the coil module (1) and configured to generate the nuclear magnetic test signal and collect the induction signal.

An exemplary coil arrangement can be provided, which can include, for example, coil element(s) having a parallel resonant circuit at a port, where the coil element(s) is detuned by causing a low impedance at the port. Pre-amplifier arrangements can provide a low impedance at the port of the coil element(s) to suppress the induced current on the coil element(s) thereby reducing the inductive coupling to neighboring element(s). The coil element(s) can include an inductance and a capacitance which cancel each other out. The inductance and the capacitance can cancel each other out such that an impedance of the coil element has no imaginary part at a working frequency. An impedance of the coil element(s) in free space includes a real part that can be greater than a sum of losses for the coil element(s).

An MRI system receive coil arrangement 3 for use with a main MRI scanner arrangement. The arrangement includes at least one primary receive coil 6 having a first impedance at a predetermined frequency and a first size defined by a cross-sectional area bounded by the primary receive coil and at least one auxiliary receive coil 7 having a second impedance at said predetermined frequency and a second size defined by a cross-sectional area bounded by the auxiliary receive coil wherein the first impedance is lower than the second impedance and the first size is larger than the second size.

A nuclear magnetic resonance apparatus for estimating properties of an earth formation includes a carrier configured to be deployed in a borehole in the earth formation and at least one transmitting assembly disposed in the carrier and configured to generate an oscillating magnetic field in a volume of interest within the earth formation. The apparatus also includes at least one receiving assembly disposed in the carrier and configured to detect a nuclear magnetic resonance (NMR) signal originating in the volume of interest. In this apparatus, the receiving assembly includes at least a first longitudinal region with a loop coil and a butterfly coil, the loop coil central axis being located over a region of the magnet assembly where a static magnetic field is predominantly along an azimuthal direction to the carrier and the butterfly coil being at least partially overlapped with the loop coil to reduce mutual coupling.

In one example, an RF coil array includes a first RF coil configured to generate a magnetic field along a first axis, the first RF coil having a first surface, a second RF coil configured to generate a magnetic field along a second axis, orthogonal to the first axis, the second RF coil having a second surface, and a first foldable interconnect coupling the first RF coil to the second RF coil. The first foldable interconnect may be adjusted to couple the first RF coil to the second RF coil with a first amount of overlap and with the first surface and second surface facing a common direction, or couple the first RF coil to the second RF coil with a second amount of overlap, larger than the first amount of overlap, and with the first surface in face to face position with the second surface.

An RF coil unit of an embodiment includes a plurality of first coil elements each having a first main loop which receives a magnetic resonance signal and a plurality of second coil elements each having a second main loop and a sub-loop protruding from a portion of the second main loop. Any combination of two coil elements chosen from the plural first coil elements and the plural second coil elements is arranged in an overlap area where areas surrounded by one and another one of the two coil elements overlap in such a way that the overlap area is located in an area surrounded by the first main loop.

The present invention provides a radio frequency (RF) coil (140) for applying an RF field to an examination space (116) of a magnetic resonance (MR) imaging system (110) and/or for receiving MR signals from the examination space (116), whereby the RF coil (140) is provided having a tubular body (142), the RF coil (140) is segmented in a longitudinal direction (154) of the tubular body (142) into two coil segments (146), and the two coil segments (146) are spaced apart from each other in the longitudinal direction (144) of the tubular body (142), whereby a gap (148) is formed between the two coil segments (146). The present invention further provides a magnetic resonance (MR) imaging system (110) comprising at least one radio frequency (RF) coil (140) as specified above. The present invention still further provides a medical system (200) comprising the above magnetic resonance (MR) imaging system (110) and a medical device (202), which is arranged to access to the examination space (116) of the magnetic resonance (MR) imaging system (110) through the gap (148) of the RF coil (140). Even further, the present invention provides a method for applying a radio frequency (RF) field to an examination space (116) of a magnetic resonance (MR) imaging system (110), comprising the steps of providing at least one above radio frequency antenna device (140), and commonly controlling the two RF coil segments (146) to provide a homogenous B.sub.1 field within the examination space (116), in particular within the gap (148).

A method of preparing a multi-channel coil, in particular for magnetic resonance imaging (MRI) or for a medical treatment device, wherein the multi-channel coil comprises at least two coil rows being axially arranged along a longitudinal direction (z), wherein each of the at least two coil rows comprises a plurality of coil elements being azimuthally distributed relative to the longitudinal direction (z), comprises the steps of a) electro-magnetic decoupling of the coil rows relative to each other, and b) minimizing a reflected power (P.sub.ref.sub._.sub.row) individually of each of the coil rows. Furthermore, a method of operating a multi-channel coil, in particular for magnetic resonance imaging (MRI) or for a medical treatment device, and a multi-channel coil, which is prepared using to the above method are described.