Abstract: Special patient handling apparatus and method retains increased accessibility advantages for open C-magnet MRI system architecture. The required volume for an accompanying RF shielded gantry room may also be minimized. The special patient transport mechanism may include a structure which at least partly telescopes around the lower pole face of the C-shaped MRI polarizing magnet as the patient is side-loaded into the image volume between the magnet pole faces. Substantially adjacent open accessibility to the patient is maintained throughout the loading procedure and throughout the subsequent preparatory and imaging procedures associated with the MRI system.

Abstract: MRI T1 relaxometry is performed using a single fixed strength magnetic background field for RF signal transmission and reception thus greatly simplifying RF circuitry design and/or adjustment. Switched differing strength background magnetic fields are employed at other times in the relaxometry cycle so as to predominate the NMR T1 relaxation parameter value and thus permit relaxometry determinations of T1 values versus magnetic field strength (or the equivalent corresponding NMR RF frequency) at N data points using as few as N+1 measurement cycles. Process and apparatus are disclosed for thus efficiently achieving in vivo NMR relaxometry (including magnetic resonance imaging if desired).

Abstract: A high T.sub.c superconductive electromagnet winding is advantageously employed as part of an MRI magnet structure having a pair of magnetically permeable poles opposingly disposed about the patient imaging volume. The magnetic circuit is otherwise completed by a magnetically permeable yoke structure having plural open apertures for easy access to the patient imaging volume. Still further advantage can be had by asymmetrically disposing a single superconductive electromagnet winding with respect to the patient image volume thereby eliminating the need for more than one cryostat. When high T.sub.c superconductive electromagnetic windings are utilized, a non-conductive composite cryostat may also be used to further reduce spurious eddy current fields. When an asymmetric single high T.sub.

Abstract: At least one imaging parameter (e.g., the repetition interval TR or the initial nutation angle .theta.) is varied during the course of a single MR image sequence. This variation in at least one imaging parameter is preferably controlled so as to increase the contrast and signal-to-noise ratio of lower spatial frequency image components. For example, by using longer TR intervals (or smaller initial nutation angle .theta.) during lower spatial frequency phase encoding sub-sequences, relatively more signal is gathered from NMR nuclei having long T1 parameters thus providing a resultant image with many characteristics of a much longer overall sequence (e.g., one using uniform relatively long TR intervals for all spatial frequency phase encoding sub-sequences).

Abstract: An auxiliary insert MRI gradient coil is used to produce intense auxiliary magnetic gradient pulses during MRI sequences to improve MRI system performance. Although the auxiliary gradient coil may be of considerably reduced dimensions, thus, having considerably reduced uniformity, linearity and/or reproducibility than standard MRI gradient coils, coordinated use of both the regular MRI gradient coils and the auxiliary gradient coil can produce considerably enhanced MRI system performance in certain applications. Such auxiliary magnetic gradient coil may be used, for example, to provide spoiler pulses between MRI spin echo subsequences, as diffusion gradient pulses in diffusion MRI studies or as the oscillating gradient used to form successive gradient echoes in echo planar imaging.

Abstract: Electromagnet coil driving circuitry in a magnetic resonance imaging system is modified to include a flux-driven closed-loop real-time feedback control. The result is more accurate and efficient control of the net actual gradient flux generated by the coil even in the presence of magnetic circuit materials exhibiting hysteresis effects and/or electrical conductors giving rise to eddy current effects. Such driver control can be used to simultaneously correct the magnetic flux changes induced by environmental, ambient or other outside disturbances affecting the net magnetic field within a patient imaging volume of a magnetic resonance imaging system.

Abstract: At least one imaging parameter (e.g., the repetition interval TR or the initial nutation angle .theta.) is varied during the course of a single MR image sequence. This variation in at least one imaging parameter is preferably controlled so as to increase the contrast and signal-to-noise ratio of lower spatial frequency image components. For example, by using longer TR intervals (or smaller initial nutation angle .theta.) during lower spatial frequency phase encoding sub-sequences, relatively more signal is gathered from NMR nuclei having long T1 parameters thus providing a resultant image with many characteristics of a much longer overall sequence (e.g., one using uniform relatively long TR intervals for all spatial frequency phase encoding sub-sequences).

Abstract: Continuously updated real-time magnetic resonance imaging processes are used to display an MR image volume to an operator and/or patient co-located with the MRI magnet, viewing console and other elements of an MRI system within the same shielded gantry room. A CRT display may be used for lower field MRI systems while liquid crystal displays may be necessary for higher field MRI systems since the viewing console is to be co-located within the shielded gantry room near the MRI magnet assembly. Suitable RF shielding is provided to RF-isolate the viewing console and its related power and video signal cables from the MRI RF coils being used to monitor relatively weak NMR signals emanating from the image volume within the magnet assembly.

Abstract: A measure of magnetic field inhomogeneity along a phase-encoded (e.g. y-axis) dimension is derived in k-space from previously acquired MRI phase-encoded projection data. From this, a measure of MRI data skewing caused by such inhomogeneity is obtained and used to compensate therefor. Since the MRI data is to be multi-dimensionally Fourier Transformed in most instances anyway, a transform in the relevant phase encoded dimension (e.g., y-axis) is taken followed with phase shifting each digitized data point by an amount proportional to the measured magnitude of inhomogeneity and to the datum coordinate in the read-out dimension (e.g., x-axis) and to the datum coordinate in each phase-encode dimension (e.g., y-axis) before the data is further Fourier Transformed with respect to the read-out dimension (e.g., x-axis). If two-dimensional phase encoding is employed (e.g., as in 3DFT), then a second level of similar inhomogeneity compensation can be had in the third dimension (e.g., z-axis) as well.

Abstract: Positioning of interventional devices within the patient image volume of an MRI system is performed while viewing real-time fluoroscopic MR images of such devices superimposed upon a saved prior image ("ghost") of patient anatomy that was earlier located within the same image volume. After such interventional medical procedure is thoroughly planned using the earlier acquired three-dimensional ghost image, the patient anatomy is relocated within the image volume and the final selected trajectory for the interventional device or medical procedure is then performed (preferably while real time MRI fluoroscopy is used to monitor the actual interventional procedure within the real patient anatomy).

Abstract: Static B.sub.o field strength is measured during each TR interval of an MRI sequence providing field calibration data used to compensate for rapid variations in B.sub.o during the MRI sequence.

Abstract: Variable voxel shifts required for shifting a 3D structure into a common oblique or contoured slice volume based on an existing 3D image are achieved by effecting variable f(x,y) phase shifts in corresponding frequency domain data parallel to a selected axis dimension and then reconstructing a new three-dimensional image having the 3D structure all located within a common oblique or otherwise contoured slice volume such that it may viewed in a single planar image display without loss of volume resolution. Equivalent convolution processes withing the spatial domain may also be empolyed. Oblique or curved reconstructions can thus be made using either originally acquired frequency domain data (used to construct the original image) or frequency domain data obtained by inverse Fourier transforming the available spatial domain data of the images themselves.

Abstract: A bridge conductors for the turns of an MRI RF coil may be connected serially within a connector joint area of an inductive coil so as to selectively increase its physical size (e.g., so as to accommodate larger patient volumes to imaged therewithin). Serial capacitance may be included in at least one of the bridging conductors so as to substantially reduce the net inductive impedance of the added bridge conductors such that the standard coil RF tuning and impedance matching circuits may still operate within their normal predetermined adjustable ranges.

Abstract: At least one extra NMR measurement cycle is performed without any imposed magnetic gradients during readout and recordation of the NMR RF response. Calibration data derived from this extra measurement cycle or cycles can be used for resetting the RF transmitter frequency and/or for phase shifting other conventionally acquired NMR RF response data to compensate for spurious changes in magnetic fields experienced during the NMR data measuring processes. Some such spurious fields may be due to drifting of the nominally static magnetic field. Another source of spurious fields are due to remnant eddy currents induced in surrounding conductive structures by magnetic gradient pulses employed prior to the occurrence of the NMR RF response signal. Special procedures can be employed to permit the compensation data itself to be substantially unaffected by relatively static inhomogeneities in the magnetic field and/or by differences in NMR spectra of fat and water types of nuclei in imaged volumes containing both.

Abstract: An array of plural magnetic resonance imaging (MRI) RF coils is provided having different and overlapping fields of view. Controllable switches are connected with each individual coil of the array and are capable of selectively conditioning any one of the coils for individual usage in an MRI procedure. Either mechanical or electrical (e.g., PIN diode) switching control may be utilized. Preferably, controllable electrical switches are located at points having approximately zero RF potential. Distributed capacitance is also preferably employed for reducing terminal inductance, preventing the establishment of spurious magnetic fields and facilitating the use of electrical switching diodes and/or varactor capacitance elements. Such distributed capacitances are also dimensioned so as to cause the terminal inductance of each coil to be within the tuning/matching range of a common tuning/matching RF circuit.

Abstract: Where short TR MRI imaging sequences are required (e.g., for contrast media imaging), NMR signal strength losses are reduced by including an extra peparatory nutation pulse at an interval TR prior to the usual nutation sequence used to elicit an NMR RF response. The "dead time" during such a TR interval for one slice is utilized for eliciting and receiving NMR RF responses from at least one other slice and sending the extra preparatory nutation pulse into yet another slice thus effecting a multi-slice procedure with an effective TR less than the actual time between repetitions of a complete multi-slice projection sequence while yet retaining high signal strength.

Abstract: An MRI system using a pair of opposed magnetic poles to create the requisite static magnetic field H.sub.o is configured so as to provide open and unobstructed patient access areas communicating directly with an MRI imaging volume along directions which are perpendicular to the patient transport axis. In this manner, operator/doctor access to the patient is maximized while potential claustrophobic reactions from the patient are minimized.

Abstract: NMR imaging apparatus and method is arranged so as elicit NMR image response data in a predetermined order which provides the more significant lower spatial frequency image data during an initial portion of a relatively long complete image data acquisition cycle. The remaining higher spatial frequency image data is captured during subsequent portions of the overall image data acquisition cycle. In this manner, apparent motion artifact in the resulting image is reduced. Furthermore, such a special data acquisition sequence permits image reconstruction processes to produce a recognizable image at an earlier time in the complete data gathering cycle thus permitting a more timely image display for the apparatus operator to use in monitoring and/or controlling the NMR imaging procedure.