Picker International, Inc.

Cleaner Food, Inc.

James M McNally

David A Lampman

Timothy B Hansen

Martyn N Paley

Gordon D DeMeester

John Lester Patrick

Haiying Liu

Paul M Margosian

Xueming Zou

James B Murdoch

Gregory C Hurst

Surya N Mohapatra

Gilbert T Williams

An irradiation apparatus particularly well suited to the irradiation of food at or near the point of consumption includes an irradiation chamber, one or more ionizing radiation sources such as x-ray tubes, and a rotating food support. In one embodiment, one or more x-ray sources are disposed axially in relation to the support. In another, one or more x-ray sources are disposed radially in relation to the support. The position of the x-ray sources in relation to the food may also be varied depending on the size of the food.

Irradiation apparatus and method

A registration system (,) for use in connection with an image guided surgery system (,) is provided. It includes a medical diagnostic imaging apparatus (,) for collecting image data from a subject (,). An image data processor (,) reconstructs an image representation of the subject from the image data. An image projector (,) depicts the image representation on the subject (,). In a preferred embodiment, the image projector (,) depicts the image representation on the subject (,) such that registration between the subject (,) and the image representation is readily apparent. Preferably, the image projector (,) is a laser lightshow projector, a projection television, or a backlit liquid crystal display device. Optionally, a data processor (,) applies corrections to the image data such that surface contours of the subject (,) are accounted for when the image is projected onto the subject (,).

Movable mirror laser registration system

A sequence control (40) causes a transmitter (24) and gradient amplifiers (20) to transmit radio frequency excitation and other pulses to induce magnetic resonance in selected dipoles and cause the magnetic resonance to be focused into a series of echoes in each of a plurality of data collection intervals following each excitation. A receiver (38) converts each echo into a data line. Calibration data lines having a close to zero phase-encoding are collected during each of the data collection intervals. The calibration data lines in each data collection interval are zero-filled (86) to generate a complete data set and Fourier transformed (88) into a series of low resolution complex images (90.sub.1, 90.sub.2, . . . 90.sub.n), each corresponding to one of the data collection intervals. The low resolution images are normalized (92) and their complex conjugates taken (94). Imaging data lines are sorted by a data collection interval and zero-filled (104) to create full data sets. The full data set corresponding to each data sampling interval is Fourier transformed into partial image representations (106.sub.1, 106.sub.2, 106.sub.n). Each partial image is multiplied (108) by a complex conjugate of the normalized phase correction map (96) to create corrected partial images which are summed (112) to generate a composite image (114). The composite images are density corrected (120).

Magnetic resonance scan calibration and reconstruction technique for

A magnetic resonance gantry (A) includes a magnet (12) which generates a uniform magnetic field in a thin (under 15 cm thick) imaging volume (10). Gradient coils (30) and radio frequency coils (20) transmit radio frequency and gradient magnetic field pulses of conventional imaging sequences into the imaging volume. A patient support surface (42) moves a patient continuously through the imaging volume as the pulses of the magnetic resonance sequence are applied. A tachometer (52) monitors movement of the patient. A frequency scaler (54) scales the frequency of the RF excitation pulses applied by the transmitter (22) and the demodulation frequency of the receiver (26) in accordance with the patient movement such that the selected slice moves in synchrony with the patient through the imaging volume. The slice select gradient is indexed after magnetic resonance signals to generate a full set of views for reconstruction into a two-dimensional image representation of the slice are generated. The views for each slice are reconstructed (28) into a three-dimensional image representation that is stored in a memory (60). By using rapid imaging techniques, such as echo-planar techniques which can generate a two-dimensional image of a slice in 150 milliseconds, a three-dimensional diagnostic image of a section of a subject one meter long can be generated in less than 2 minutes.

Magnetic resonance imaging system with thin cylindrical uniform field

Superconducting magnets (10) of a magnetic resonance imager create static magnetic fields through an examination region (12). Gradient magnetic field coils (30) under control of a gradient magnetic field control (42) generate gradient magnetic fields across the examination region (12), as a whole. A plurality of surface coils (36, 38) receive radio frequency signals from each of two distinct subregions within the examination region (12). The two receiver coils are connected with separate receivers (60.sub.1, 60.sub.2) which demodulate the received magnetic resonance signals. The magnetic resonance signals are reconstructed (76) into an image representation (80, 82) of the first and second subregions. In the embodiment of FIGS. 1 and 2, a radio frequency transmitter (40) and a whole body coil (32) generate and manipulate the magnetic resonance signals within the first and second subregions. In the embodiment of FIGS. 3 and 4, a plurality of transmitters (40.sub.1, 40.sub.2, . . . ) convey RF signals to the surface coils such that the surface coils operate in both a transmit and receive mode. Regardless whether a single transmitter or a series of transmitters is utilized, a sequence control (44) controls the transmitter(s) and the gradient control (42) to conduct conventional magnetic resonance imaging sequences in coordination in both subregions.

Simultaneous magnetic resonance imaging of multiple human organs

RF and gradient pulse combinations (30, 32, 36, 38) are applied to limit or define a region of interest in two dimensions (42) by pre-saturating surrounding regions (34a, 34b, 40a, 40b). A 90.degree. RF pulse (50) is applied in the presence of a slice select gradient (60) to excite selected dipoles in a slice or slab, defining the region of interest or voxel in the third dimension. Phase encoding gradients (62) and (64) are applied to encode spatial position in two dimensions of the slice. A binomial refocusing pulse (52) suppresses the water and refocuses the metabolite resonance into an echo which is acquired (68) by a receiver (26). A Fourier transform means (72, 74) transforms the received magnetic resonance signals to create a two dimensional array (76) or matrix of spectra (78) corresponding to a two dimensional array of spatial positions within the slice. A third phase encode gradient (66) may be applied to encode the regionof interest in three dimensions for generating a three dimensional array of the spectra.

Multi-axis pre-saturated spin echo phase encoded spectroscopy

Magnetic resonance is excited in first selected dipoles and suppressed in second selected dipoles in an examination region (10) by the application of a binomial 90.degree. pulse (40). The induced resonance is phase encoded along at least two axes by phase encode gradients (42, 44). Concurrently, an RF refocussing pulse (54) and a slice select gradient pulse (56) are applied. Analogous pulse pairs (68, 70; 72, 74) are applied once with the slice select gradient along each of three mutual orthogonal axes such that a voxel or volume defined by the intersection of the three slices is defined. A magnetic resonance echo (84) is allowed to form, which echo is attributable to the resonating dipoles within the defined voxel. The phase encoding gradients have divided the voxel into subvoxels along the respective axes. The resultant magnetic resonance echo signals are Fourier transformed (92) into sets of chemical spectra corresponding to each subvoxel and displayed in a two dimensional image representation on a video monitor (96).

NMR spectroscopy with phase encoding within a selected voxel

A binomial pulse generator (32) selectively generates binomial radio frequency excitation pulses (60) which induce magnetic resonance only in selected hydrogen dipoles and suppresses resonance in others. An inversion pulse generator (34) generates a first inversion pulse (70) in the presence of a first magnetic field gradient (72) generated by a gradient control (22). The inversion pulse only inverts the magnetization of resonating nuclei in a first plane defined by the first magnetic field gradient. A second inversion pulse (74) applied in the presence of a second magnetic field gradient (76) inverts the magnetization of resonating nuclei in a second planar region defined by the second magnetic field gradient. A third inversion pulse (78) applied concurrently with a third magnetic field gradient (80) inverts the magnetization of resonating nuclei in a third planar region defined by the third magnetic field gradient. Only resonating nuclei in a volumetric element defined at the intersection of the first, second, and third planes are inverted all three times. The magnetization of other dipoles will have dephased differently from the dipoles in the volumetric element. In this manner, only the dipoles in the volumetric element contribute to a spin echo (82) which follows the third inversion pulse. Data acquired during the third spin echo may be spectrographically analyzed to determine the chemical composition within the volumetric element. Alternately, a phase encoding gradient (90) and a read gradient (92) may be applied as part of the sequence to provide the appropriate phase encoding to the acquired data such that the acquired data can be reconstructed into an image representation.

Growing community of inventors

Chagrin Falls, OH, United States of America

James M McNally