Abstract: When correcting for attenuation in a positron emission tomography (PET) image, a magnetic resonance (MR) image (24) of a subject is generated with spectroscopic data (38) describing the chemical composition of one or more of the voxels in the MR image. A table lookup is performed to identify a tissue type for each voxel based on the MR image data and spectral composition data, and an attenuation value is assigned to each voxel based on its tissue type to generate an MR attenuation correction (MRAC) map (30). The MRAC map (30) is used during reconstruction of the nuclear image (37) to correct for attenuation therein. Additionally, attenuation due to MR coils and other accessories that remain in a nuclear imager field of view during a combined MR/nuclear scan is corrected using pre-generated attenuation correction maps that are applied to a nuclear image after executing an MR scan to identify anatomical landmarks, which are used to align the pre-generated attenuation correction maps to the patient.

Abstract: When correcting for attenuation in a positron emission tomography (PET) image, a magnetic resonance (MR) image (24) of a subject is generated with spectroscopic data (38) describing the chemical composition of one or more of the voxels in the MR image. A table lookup is performed to identify a tissue type for each voxel based on the MR image data and spectral composition data, and an attenuation value is assigned to each voxel based on its tissue type to generate an MR attenuation correction (MRAC) map (30). The MRAC map (30) is used during reconstruction of the nuclear image (37) to correct for attenuation therein. Additionally, attenuation due to MR coils and other accessories that remain in a nuclear imager field of view during a combined MR/nuclear scan is corrected using pre-generated attenuation correction maps that are applied to a nuclear image after executing an MR scan to identify anatomical landmarks, which are used to align the pre-generated attenuation correction maps to the patient.

Abstract: A transverse electromagnetic (TEM) coil is provided. The TEM coil includes an electrically conductive shell and an end plate disposed at a first end of the shell. The TEM coil also includes a plurality of TEM elements disposed within the shell, the plurality of TEM elements being shorter than the shell.

Abstract: Multi-slice magnetic resonance imaging of a region of interest of an imaging subject (16) is performed using a radio frequency coil (40) arranged to generate a B1 magnetic field in the region of interest. One or more processors (44, 82, 88, 110) determine a B1 field value for each slice that is representative of the B1 field over a selected area of the slice, accounting for subject effects on the BI field, and determine an adjusted per-slice radio frequency excitation for each slice that adjusts the B1 field value for the slice to a selected value. A magnetic resonance imaging system (10, 44, 46, 50, 52) acquires magnetic resonance imaging data for each slice using the adjusted per-slice radio frequency excitation for that slice. A reconstruction processor (58) reconstructs the acquired magnetic resonance imaging data into a reconstructed image representation.

Abstract: An MRI apparatus is provided. The apparatus includes a main magnet for generating a main magnetic field in an examination region, a plurality of gradient coils for generating gradient fields within the main field, an RF transmit coil for transmitting RF signals into the examination region and exciting magnetic resonance in a subject disposed therein in accordance with a plurality of imaging parameters, the transmitted RF signals having a SAR associated therewith, and a SAR processor for maintaining the transmitted RF signals below a prescribed SAR level.

Abstract: A gradient coil for a magnetic resonance imaging apparatus (10) includes a primary coil (16) defining an inner cylindrical surface (60), and shield coil (18) or coils defining a coaxial outer cylindrical surface (62). Coil jumps (74) connect the primary and shield coils (16, 18). The coil jumps (74) define a non-planar current-sharing surface (64) extending between inner and outer contours (66, 68) that coincide with the inner and outer cylindrical surfaces (60, 62), respectively. The coil (16, 18, 74) defines a current path that passes across the current sharing surface (64) between the inner and outer contours (66, 68) a plurality of times. Optionally, some primary coil turns (70) are electrically interconnected to define an isolated primary sub coil (P2) that together with a second shield (S2, S2?, S2?) enables a discretely or continuously selectable field of view.