Abstract: A toroidal housing (18), such as a vacuum dewar, contains magnets (10, 12) for generating a temporally constant magnetic field through a central bore (14). Gradient coils (32, 42) are mounted around the bore defining a space therebetween. A radio frequency shield (78) is disposed radially inward from the gradient coils. Inside the radio frequency shield, an inner shimming assembly (60) includes a dielectric cylinder (62) having annular grooves around its periphery. Segmented ferrous material (66) is arranged in annular rings in the grooves. The ferrous material is segmented into small pieces electrically insulated from each other to limit radio frequency and gradient frequency eddy currents. A radio frequency coil (70) is mounted inside of the annular ferrous shims (66). Preferably, additional shim trays (50) which carry shims (54) are mounted in the space between the primary and secondary gradient coils.

Abstract: Superconducting magnets (10) generate a temporally constant magnetic field through a bore (12). The bore, hence the superconducting magnets, have a length which is relatively short compared to its diameter, a length to diameter ratio of less than 1.0 to 1.5 and preferably 1:1. A gradient coil assembly (30) is disposed around the bore for generating gradient magnetic fields across the bore. With such a relatively short bore magnet, in the region in which the gradient field coil is disposed, the main magnetic field suffers non-uniformities including radial magnetic field components. When current pulses are fed through the windings of a primary gradient coil (32) and a secondary gradient coil (34), the currents interact in an unbalanced manner with the non-uniformities and radial components of the temporally constant magnetic field, causing a net force in axial and/or transverse directions.

Abstract: A birdcage coil (42) and a quadrature coil pair which are disposed in a partially overlapping but electrically isolated relationship within a static magnetic field generated by a main field magnet (10). The birdcage coil preferably has twelve legs, has eight-fold symmetry, and is tuned to have two linear modes aligned with first and second orthogonal axes. The quadrature coil includes a first or upper coil portion (90) having an even-number of legs and a mode aligned with a third axis. A second or bottom quadrature coil (92) has an odd-number of legs and has a mode which is aligned with a fourth axis, preferably orthogonal to the third axis. Received resonance signals of the two modes of the birdcage coil are combined (66) and digitized (64); resonance signals received in the first and second modes of the quadrature coil pair are combined (66) and digitized (64).

Abstract: A subject is positioned on a patient support (12) between an x-ray source (10) and a radiation detector assembly (14). The x-ray source is gated (36) on or open prior to triggering (38) a video camera (26) of the x-ray detector assembly to generate an electronic frame image representation. The patient support is moved to generate reference images at positions (5, 4, 3, 2, 1) and the resultant reference images are stored in a reference image memory (42). A radiopaque dye is injected adjacent a first position (1) and the x-ray source and camera are triggered at a first rate indicated by a scan program memory (50). The generated images are displayed on a video monitor until a radiologist decides that the radiopaque dye has moved downstream sufficiently that it is time to index to a second position (2). The radiologist presses an index button (68) causing the patient to be indexed.

Abstract: An x-ray source (12) is mounted to a rotatable gantry (16). The x-ray source irradiates an examination region (14) with penetrating radiation as (i) the x-ray source rotates around the examination region and (ii) a patient coach (30) moves a patient axially through the examination region. Detectors (24) positioned on an opposite side of the examination region converts radiation which has traversed the examination region along spiral paths (80). Data from the detectors are collected and stored (40) in spiral data sets. In the prior art spiral data on either side of a thin slice central plane was interpolated into a thin slice data set, each thin slice data set was reconstructed into a thin slice image, and several thin slice images were combined to make a thick slice image with significant partial volume artifacts. By distinction, an integrating interpolator (42) weights (88) data values in several spiral sets in accordance with a weighting values W.sub.1, W.sub.2, . . .

Abstract: In a magnet system, e.g. for use in a magnetic resonance apparatus, wherein a magnetic field is produced in a gap between pole pieces (5) joined by a yoke (7) by an electric drive coil arrangement carried on the yoke, stabilisation against variations in the field in the gap is provided by a stabilising arrangement (43) wherein over a section of its length the yoke is divided into a plurality of discrete parallel finger-like portions (45) each of which is surrounded by a separate ring (47) of superconducting non-magnetic material.

Abstract: A subject receiving bore (12) of a magnetic resonance apparatus has an axial length to diameter ratio of less than 1.75:1 and preferably about 2:1. The temporally constant magnetic field generated by superconducting magnets (10) surrounding the bore have various magnetic field harmonic distortions generally in the Z1-Z18 range. Shim trays (80) are disposed longitudinally around the bore (12). Each shim tray contains a number of shim pockets (84) which receive ferrous shims for shimming the magnetic field in the bore (12). An initialization system (60) calibrates the initial magnetic field within the bore (12). An initial shim distribution is determined which shims the inhomogeneous magnetic field toward a target more homogeneous magnetic field. An optimization system (66) determines a residual magnetic field from a difference between the present inhomogeneous magnetic field of the bore and the target magnetic field.

Abstract: Magnetic resonance imaging data of a volume of interest is collected by applying a radio frequency pulse (70, 96) and following the pulse with gradients applied along three axes (x,y,z). The gradients along x and y-axes are generally sinusoidal, which sinusoids increase and decrease in magnitude to define beat patterns of a common period. The period of the first and second gradients is an integer multiple of the gradient along the z-axis. In the embodiment of FIGS. 2A and 2B, the beats of the first and second gradients increase linearly and the third gradient oscillates in a linearly expanding generally sinusoidal pattern such that k-space is traversed by a trajectory that spirals around a series of spheres (50, 52, 54, 56, 58, 60) of progressively smaller radius. Blips or spikes (78) are preferably applied between each half cycle of the third gradient to step the trajectory to the radius of the next concentric sphere. In the embodiment of FIGS.

Abstract: An examination region (34) is divided into a multiplicity of slices, e.g. slices 1-20. The slices are divided up into groups or slabs, e.g., slabs I-V. A series of magnetization inversion pulses (70.sub.I- 70.sub.V) and slab select gradient pulses (74.sub.I -74.sub.V) are applied at regular intervals. At a duration after each slab inversion at which the magnetization of a material such as CSF is at a minimum or null (80) marks a center of a data acquisition period (84). A plurality of imaging sequences (82) are conducted in each data acquisition period. Each of the imaging sequences collects one or more data lines from each of the slices within the corresponding slab. This process is repeated cyclically until all of the data lines of each slice of each slab have been collected. The data lines are reconstructed (102) into an image representation which is stored in an image memory (104) for selective display on a video monitor (108).

Abstract: A object handling system is moveable between various diagnostic imaging apparatus for imaging thereby. The handling system has an object handling computer 34 for storing object identification data and imaging data. Selectively linking the object handling computer 34 with a first imaging system provides the first imaging system with access to the object identification data and imaging data for use in the production of diagnostic images thereby. Similarly, the object identification data and imaging data are available to a second imaging system for use in the production of diagnostic images thereby when the object handling computer 34 is selectively linked thereto. The object identification data is associated with the diagnostic images produced by various imaging system for subsequent correlation of the object with the diagnostic images of the object.

Abstract: A three head SPECT camera system has three detector heads (22a, 22b, 22c) disposed at 120.degree. intervals. Two of the detector heads have collimators (40a, 40b) which have a first set of vanes (42a, 42b) extending in a direction parallel to an axis of rotation (26) but which are canted 15.degree. relative to a perpendicular, central axis (32a, 32b) of the respective detector heads. A second set of vanes (46a, 46b) extend perpendicular to the 15.degree. tipped set of vanes to define a rectangular grid. When the second set of vanes is perpendicular to the detector heads, the first detector head is constrained to receive radiation along a first plurality of parallel rays (44a) and the second radiation detector head is constrained to receive radiation along a second plurality of parallel rays (44b). The collimators are mounted to the detector head such that the first and second parallel rays (44a, 44b) are perpendicular to each other. In this manner, a full 180.degree.

Abstract: Magnetic resonance is excited in selected portions of a subject disposed within a temporally uniform magnetic field of a magnetic resonance imaging system. A quadrature coil assembly (30) receives radio frequency magnetic resonance signals from the subject. Commonly, the quadrature coil fails to receive signals in true quadrature over the entire examination region. Resonance signals from a first coil (32) and a second, orthogonal coil (34) are received (40, 42), digitized (44, 46), and Fourier transformed (50, 52) into complex images. Each complex image includes an array or grid of vector data values having a magnitude and a direction or phase angle. If the quadrature coil was truly quadrature over the entire region of interest, the data values of both complex images would be a unit vectors. The vector of one image would be offset by 90.degree. from the vectors of the other.

Abstract: An x-ray tube (14) has an evacuated envelope (30) in which an anode (32), a cathode (34), and a getter shield (60) are disposed. The shield includes a sleeve (62) and a cap (64). The cap defines an annular groove (70). A getter material (72) is deposited in the groove and sintered to define a porous volume. The getter material is activated during normal exhaustion of the x-ray tube during manufacture. During operation of the tube to generate x-rays, the waste heat is absorbed by the cap passively raising the getter material to its pumping temperature.

Abstract: Magnets (12) create a temporally constant magnetic field through an examination region (14). Radio frequency coils (26, 34) and a transmitter (24) transmit radio frequency saturation pulses (52) and the resonance excitation and manipulation pulses of a magnetic resonance imaging sequence (72) into the examination region. Gradient amplifiers (20) and gradient coils (22, 32) create magnetic field gradients across the examination region for spatially focusing the saturation, for spoiling (62, 66, 70) residual transverse magnetization and for frequency and phase encoding in the magnetic resonance imaging sequence. A sequence controller (40) includes a saturation pulse controller (44) for generating the saturation pulse (52) and slice select gradients (58) and a steady state sequence controller (48) for generating the imaging sequence (72). The saturation is spectrally focused by limiting the frequency of the saturation pulse to selected frequencies.

Abstract: An insertable coil (40) is inserted in a bore (12) of a magnetic resonance imaging apparatus. Primary field magnets (10) create a temporally constant magnetic field longitudinally through the insertable coil. A computer control (58) controls a radio frequency coil (44) and a gradient coil (42) to create magnetic resonance imaging sequences and process received magnetic resonance signals into image representations. The insertable gradient coil includes a central cylindrical portion (60) having a first circumference. A second portion (62) disposed toward a patient receiving end of the insertable coil has a second circumference which is larger than the first circumference. In this manner, the first, smaller circumferential portion is adapted to receive the patient's head and the larger circumferential portion is adapted to accommodate the patient's shoulders. For symmetry which eliminates magnetic field induced torques, a service end (68) matches and is symmetric to the patient end (62).

Abstract: A toroidal x-ray tube (I) is supported and selectively positioned by a gantry (II). The x-ray tube includes a toroidal housing (A) in which a rotor (20) is rotatably mounted. One or more cathodes (C) are mounted on the rotor for generating an electron beam which strikes an anode (B) to generate a beam of x-rays which pass through a patient aperture (62) to strike a detector (60). The x-ray tube includes pre-collimators (70, 74) having slots (72, 76) for passage of the x-ray subsequent to generation thereof and prior to being collimated by the collimator (90). A ring collimator (90) collimates an x-rays formed into a fan shaped beam. The collimator (90) includes a first ring (92) and a second ring (94) which are concentric. The distance between the first and second rings (92, 94) is adjustable to adjust the slice thickness of the final image.

Abstract: A magnetic resonance imaging apparatus defines an examination region (14) within which main magnets (10) create a uniform magnetic field. Magnetic resonance is excited in dipoles of a subject within the examination region causing the generation of magnetic resonance signals that are received by either a localized coil (C) or whole body radio frequency coils (22). The radio frequency coils are disposed sufficiently adjacent the examination region that the coils are subject to magnetic fields and magnetic field gradients, that any ferrous metals would alter the magnetic field. Magnetic resonance signal processing circuits (54) which are mounted on the coil are free of ferrous materials, such as iron and nickel, to prevent distortion of the uniform magnetic field. The circuit includes an array of unpackaged component dice which are free of ferrous or other packaging.

Abstract: A CT scanner (10) has an x-ray source (12) which transmits a plurality (N) of x-ray fans across an examination region (14) to a plurality of rings of radiation detectors (28). An adjustable septum (80) adjusts a gap between the fan beams and outer collimators (82) adjust the width of the fan beams such that the effective spacing and width are adjusted. The x-ray source rotates around the examination region as a subject support (32) moves longitudinally through the examination region such that the x-ray fans move along interleaved spiral trajectories. Radiation attenuation data from each of the x-ray fans is combined and reconstructed into a plurality of images along parallel slices orthogonal to the longitudinal axis. The spacing between the x-ray beams is adjusted relative to the effective pitch of the spirals such that the leading edges of the x-ray fans intersect a common transverse plane at 180.degree./N angular intervals around the longitudinal axis.

Abstract: An insertable coil (40) is inserted in a bore (12) of a magnetic resonance imaging apparatus. Primary field magnets (10) create a temporally constant magnetic field longitudinally through the insertable coil. A computer control (58) controls a radio frequency coil (46) and a gradient coil (42) to create magnetic resonance imaging sequences and process received magnetic resonance signals into image representations. The insertable gradient coil includes a cylindrical, dielectric former (44) of appropriate diameter to receive a patient's head. A pair of parabolic cutouts (62) are defined adjacent a patient receiving end of the dielectric former and are of an appropriate size to receive the patient's shoulders. In this manner, the patient's head can be centered in a longer head coil. Four thumbprint type x-gradient coil windings (72) are mounted symmetrically on the dielectric former with the parabolic cutouts (74) centrally on one side of the thumbprint coil windings.

Abstract: X-ray detectors (24) of a CT scanner (10) generate data values which are preprocessed and assembled (26) into binary data lines. The binary data lines are convolved by a convolver (30) which convolves a plurality of data lines concurrently. A backprojector (32) includes a parametric cubic spline preinterpolator (40) which performs a high order interpolation on the convolved data lines and a linear interpolator (42) which performs a linear interpolation on the high order preinterpolated data lines. The interpolated data lines are backprojected into an image memory (34). Data from the image memory (34) is converted (36) to appropriate format for display on a video monitor (38). The parametric cubic spline preinterpolator (40) includes a first adder (52) which adds most adjacent data lines and a second adder (54) which adds next most adjacent data lines. A first barrel shifter (58) shifts the binary sum of the most adjacent data lines by 1-N spaces, where N is an integer, 4 in the preferred embodiment.