Abstract: A multi-modality system (10) includes a nuclear imaging system (12) and a computed tomography (CT) scanner (14). The nuclear system (12) includes a PET scanner (28) which acquires electronic data that is reconstructed into a PET blob image by a PET reconstruction processor (50). The CT scanner (14) acquires the scanned data which is reconstructed into a 3D CT voxel image by a CT reconstruction processor (56). An interpolation processor (62) interpolates the PET blob image directly into the CT voxel space. Once the PET and CT images are in the same space, they are combined by a combining means (110). A video processor (66) processes the received composite PET-CT data for a display on a monitor (68).

Abstract: A gamma ray detector module that includes at least one crystal element arranged in a plane, a plurality of light sensors arranged to cover the at least one crystal element and to receive light emitted from the at least one crystal element, and a light guide arranged between the at least one crystal element and the light sensors, the light guide being optically connected to the at least one crystal element. Further, the light guide includes a narrow portion that positions at least one light sensor of the plurality of light sensors closer to the at least one crystal element than other light sensors of the plurality of light sensors. In addition, the light guide may include an angled recessed portion that positions another light sensor at an oblique tilt angle with respect to the plane of the at least one crystal element.

Abstract: A diagnostic imaging device includes detector elements (16) for detecting y-rays indicative of nuclear decay events. Pairs of concurrently detected ?-rays define lines of response (LORs) which are collected, time stamped, and compiled in list-mode. In tissue perfusion studies, it is beneficial to use the data that concurrently maximizes contrast and signal-to-noise ratio in the reconstructed images. Using the list-mode data, events in an adjustable temporal window (33) are reconstructed and the reconstructed images are analyzed to determine a figure of merit based on contrast and signal-to-noise properties of the image. By iteratively adjusting the temporal window, extending its start point (36) backwards in time, and repeating the reconstructing, analyzing, and adjusting steps, an image with an optimal figure of merit is obtained.

Abstract: A method of processing positron emission tomography (PET) information obtained from a PET detector having a plurality of detector regions, each detector region having at least one detector module and a corresponding regional collector, the method including the steps of receiving PET event information for a single PET event, the PET event information including energy information and crystal position information of the single PET event; receiving non-detector event information; generating an event list that includes (1) a PET event entry, the PET event entry including a fine time stamp, the energy information, and the crystal position information, and (2) a non-detector event entry that includes the received non-detector event information; and transmitting the generated event list to a computer for off-line processing.

Abstract: A positron emission tomography (PET) scanner system, including a detector that acquires PET event information, the detector being configured to move during acquisition of the PET event information; a first motion unit that acquires first event information of a position of a patient bed, the patient bed being configured to move during acquisition of the PET event information; a second motion unit that acquires second event information of the detector; an event collector that generates an event list of events that includes the PET event information, the first event information, and the second event information; and a list-mode reconstructing unit that reconstructs an image by processing the generated event list.

Abstract: A diagnostic imaging device includes detector elements (16) for detecting ?- rays indicative of nuclear decay events. The detected ?-rays are used to produce lines of response (LORs) (46), which are time stamped (20) and stored in list mode. The LORs are reconstructed (34) into an image. An image analysis processor (38) analyzes the image for motion artifacts and iteratively adjusts an event transform processor (30) to transform selected LORs to minimize the motion artifacts. If the transformed LOR (50) does not correspond with a pair of detector elements (16), closest detector elements (52, 54) are determined. Candidate LORs (62) are created between the closest and neighboring detector elements. An event location (40) on an LOR (46) is determined from the time-of-flight (TOF) information and then transformed (47) to generate a transformed event location (48).

Abstract: A positron emission tomography detector module that includes an array of optically isolated crystal elements and photomultiplier tubes that receive light emitted from the array of crystal elements and are arranged to cover the array of crystal elements. The photomultiplier tubes include photomultiplier tubes having two different sizes arranged in various patterns that minimize the number of edges. The axial extent of each detector module is at least three times longer than the other axis of the detector module.

Abstract: When compensating for truncated patient scan data acquired by a multi-modal PET/CT or PET/MR imaging system (14, 16), such as occurs when a patient is larger than a field of view for an anatomical imaging device, a segmented contour of a non-attenuation-corrected (NAC) PET image is used to identify a contour of the truncated region. An appropriate tissue type is used to fill in truncated regions of a truncated CT or MR image for the attenuation map. The corrected attenuation map is then used to generate an attenuation-corrected PET image of the patient or a region of interest. Alternatively, the system can be employed in PET/CT or PET/MR imaging scenarios where two modalities are performed sequentially (e.g., not simultaneously), and thus the contour derived from the PET scan can be compared to the CT or MR image to infer potential subject motion between the PET and CT or MR scans.

Abstract: When performing positron emission tomography (PET) scanning and image reconstruction, a primary PET system (10) with a primary PET detector array (12) is used to image a patient or subject, and a secondary PET detector array (14) is coupled to the system at specific input points to mitigate unnecessary duplication of system components. The primary system (10) provides PET data processing and reconstruction for the secondary array (14), in addition to the first array (12). An adjustable array (120) includes radially movable detectors (122) and stationary detectors (124) with different crystal resolutions. The movable detectors (122) are alternately positioned with the stationary detectors (124) at a first radius to form a large detector ring, or are positioned at a second, smaller radius without the stationary detectors (124) to form a small detector ring.

Abstract: A laser induced breakdown spectroscopy (LIBS) system uses discrete optical filters for isolated predetermined spectral components from plasma light created by ablation of a sample. Independent detection elements may be used for detecting the magnitude for each spectral component. A first spectral component may include a characteristic wavelength of the sample, while a second spectral component may be a portion of a background continuum. The filters may include volume Bragg gratings and the detectors may be photodiodes. A detector that detects plasma light remaining after the isolation of the predetermined spectral components may be used together with a signal acquisition controller to precisely control the initiation and termination of signal acquisition from each of the detection elements. The system may also have optics including a collimating lens through which passes both the initial plasma light and the isolated spectral components.

Abstract: Methods, systems and apparatuses for processing data associated with nuclear medical imaging techniques are provided. Data is ordered in LUT's and memory structures. Articles of manufacture are provided for causing computers to carry out aspects of the invention. Data elements are ordered into a plurality of ordered data groups according to a spatial index order, and fetched and processed in the spatial index order. The data elements include sensitivity matrix elements, PET annihilation event data, and system and image matrix elements, the data grouped in orders corresponding to their processing. In one aspect geometric symmetry of a PET scanner FOV is used in ordering the data and processing. In one aspect a system matrix LUT comprises total number of system matrix elements equal to a total number of image matrix elements divided by a total number of possible third index values.

Abstract: Disclosed is a triple-sensor motion detector for illuminating the approach to a display case or other object. The triple-sensor motion detector provides a field of detection that spans the front width of the case, yet does not include the areas along the sides of the case. The detector reduces inadvertent triggering of the illumination by persons approaching the side of the case or approaching another case on the other side of an aisle.

Abstract: An imaging method comprises: acquiring magnetic resonance data of a subject using a magnetic resonance component (30, 30?) disposed with the subject; acquiring nuclear imaging data of the subject with the magnetic resonance component disposed with the subject; determining a position of the magnetic resonance component respective to a frame of reference of the nuclear imaging data; and reconstructing the nuclear imaging data (60) to generate a nuclear image (62) of at least a portion of the subject. The reconstructing includes adjusting at least one of the nuclear imaging data and the nuclear image based on a density map (46) of the magnetic resonance component and the determined position of the magnetic resonance component respective to the frame of reference of the nuclear imaging data to correct the nuclear image for radiation absorption by the magnetic resonance component.

Abstract: A notch filter system, where multiple filter passes of a light signal may be effected for removing a target spectral component from the light signal, is provided. Advantageously, the notch filter system may be tunable. A cascade notch filter system is provided which includes multiple notch filters arranged in a cascade, each of the filters having spectral filtering characteristics and being disposed in the path of the light signal at an appropriate filter angle so that the target spectral component is filtered out of the light signal as the light signal passes therethrough. A multipass notch filter system is provided which includes a notch filter having spectral filtering characteristics, and an optical assembly for directing the light signal for multiple filter passes through the filter at an appropriate angle, so that the target spectral component is filtered out of the light signal as the light signal passes through the filter.

Abstract: An apparatus includes a scanner (102, 104) and a scanning motion monitor (100). A motion modeler (116) uses data from the scanning motion monitor (100) and the scanner (102, 104) to generate a motion model which describes motion of a region of interest of an object. A treatment planner (112) uses image data from the scanner (102, 104) to establish a treatment plan for the object. A treatment device 114, which operates in conjunction with a treatment motion monitor (108), uses the motion model to compensate for motion of the object during application of the treatment.

Abstract: An imaging system comprises: a ring of positron emission tomography (PET) detectors; a PET housing at least partially surrounding the ring of PET detectors and defining a patient aperture of at least 80 cm; a coincidence detection processor or circuitry configured to identify substantially simultaneous 511 keV radiation detection events corresponding to electron-positron annihilation events; and a PET reconstruction processor configured to reconstruct into a PET image the identified substantially simultaneous 511 keV radiation detection events based on lines of response defined by the substantially simultaneous 511 keV radiation detection events.

Abstract: In a diagnostic imaging system (10), a monitor (50) monitors periodic biological cycles of the subject (14). A trigger point detector (60) detects a time (t1, t2, . . . ,tn) of a common, reoccurring reference point (R1, R2, . . . ,Rn) in each periodic cycle of the subject (14). A sequence selector (62) selects a sequence (64) of nominal sampling segments (Si, S2, . . . ,Sn). An adjustor (70) adjusts duration of each nominal sampling segment (Si, S2, . . . ,Sn) to coincide with the times of detected reference points (R1, R2, . . . ,Rn). A scaling processor (72) scales each adjusted segment based on a difference in duration between the corresponding nominal (Si, S2, . . . Sn) and adjusted sampling segments (S?i, S?2, . . . ,S?n).

Abstract: A hybrid imaging system and a patient bed for same are disclosed. The hybrid imaging system includes a magnetic resonance scanner and a second modality imaging system spaced apart from the magnetic resonance scanner by a gap. In some embodiments, the gap is less than seven meters. The patient bed is disposed at least partially in the gap between the magnetic resonance scanner and the second modality imaging system, and includes a linearly translatable patient support pallet aligned to be selectively moved into an examination region of the magnetic resonance scanner for magnetic resonance imaging and into an examination region of the second modality imaging system for second modality imaging. In some embodiments, a linear translation range of the linearly translatable pallet is less than five times a length of the patient support pallet along the direction of linear translation.

Abstract: An imaging system (10) comprises a data device (30), which controls radiation data acquisition from a subject positioned in an examination region (18) for an examination. A rebinning processor (40) bins the acquired data periodically into a histogram (42). A transform (70) transforms the histogram (42) into individual independent or uncorrelated components, each component including a signal content and a noise content. A stopping determining device (52) compares an aspect of at least one selected component to a predetermined threshold (TH) and, based on the comparison, terminates the data acquisition.

Abstract: A multi-modality system (10) includes a nuclear imaging system (12) and a computed tomography (CT) scanner (14). The nuclear system (12) includes a PET scanner (28) which acquires electronic data that is reconstructed into a PET blob image by a PET reconstruction processor (50). The CT scanner (14) acquires the scanned data which is reconstructed into a 3D CT voxel image by a CT reconstruction processor (56). An interpolation processor (62) interpolates the PET blob image directly into the CT voxel space. Once the PET and CT images are in the same space, they are combined by a combining means (110). A video processor (66) processes the received composite PET-CT data for a display on a monitor (68).