Abstract: When performing image-guided biopsy of an anatomical structure in a patient, a target anatomical patient region containing biopsy target is imaged using both SPECT and XCT concurrently. 3D SPECT and XCT image data is fused to generate a fused 3D reference image that is overlaid on 2D patient image(s) generated during the biopsy procedure to generate an overlay image. The overlay image also includes a planned path or trajectory for a biopsy instrument. The 2D patient images are generated using SPECT and/or XCT, and are updated periodically to show biopsy instrument position and progress.

Abstract: When performing nuclear (e.g., SPECT or PET) and CT scans on a patient, an imaging system (10) includes three or more carbon nanotube x-ray sources (20) are circumferentially spaced along an arc of a rotatable gantry (16) that spans a distance larger than a maximum cross-sectional dimension of a section of a patient (14) to be imaged. The x-ray sources are sequentially pulsed to emit x-rays for scanning a section of a patient (14) including a volume of interest (VOI) (13). Only one source (20) is in an ON state at a time to create a duty cycle, which reduces cooling time for the respective sources as well as radiation dose to the subject. X-rays traversing the patient (14) are received at a flat panel x-ray detector (22) that has a width smaller than the maximum cross-sectional dimension, which further reduces the weight and size of the system (10).

Abstract: A detector arrangement providing imaging information at the edge of the scintillator is provided. The detector arrangement provides complete information and improved spatial resolution. SiPMs can be used in place of PMTs in order to provide the geometrical coverage of the scintillator and improved spatial resolution. With such detector arrangements, the spatial resolution can be under 2 mm. Furthermore, the overall thickness of the detector can be substantially reduced and depth of interaction resolution is also improved.

Abstract: A radiation detector module for use in nuclear medical imagers employing radiation transmission or radiopharmaceuticals includes a rigid, optically opaque grid defined around a plurality of scintillator crystals. The grid defines a plurality of cells in which each scintillator crystal is completely disposed within in such a manner that an air layer exists between the scintillator crystal and the walls of the grid. A plurality of photoelectric detectors, each of which is associated with a corresponding scintillator crystal, are optically coupled to corresponding scintillator crystals by an optical coupling layer disposed within the cell.

Abstract: A nuclear imaging system includes a scanner (8), such as a PET scanner. A patient is injected with a [13N]ammonia radioisotope tracer which is contaminated with a small percent of 18F contamination. The scanner receives radiation from the injected tracer and a reconstruction processor (28) reconstructs the detected radiation into image representations. A calibration processor (16) generates an estimated decay curve based on the proton bombardment and a priori information about the tracer. An activity meter (42) measures radiation emitted from a sample of the tracer and a dose calibrator (44) determines a decay curve from the measured radiation. The detected radiation is corrected with one of the decay curves during reconstruction or a correction processor (50) corrects reconstructed images with one or both of the decay curves. A display (14) displays uncorrected reconstructed images and the decay curve and/or the corrected images.

Abstract: A imaging system for acquiring an image of a subject comprising a gantry (810) having a plurality of detection modules (812). Each detection module comprising a radiation detector and a collimator adjacent a radiation receiving face of the detector. The collimator comprises a plurality of spaced slats and a body adjacent the slats which defines at least one elongated slit extending in an axial direction (824). The slit is arranged such that radiation (822) passes through the slit and between the slats to the detector. The body is opaque to the radiation. The detection modules have a common focus (820) and do not move during acquisition of the image.

Abstract: A nuclear imaging system includes a scanner (8), such as a PET scanner. A patient is injected with a [13N]ammonia radioisotope tracer which is contaminated with a small percent of 18F contamination. The scanner receives radiation from the injected tracer and a reconstruction processor (28) reconstructs the detected radiation into image representations. A warning generator (12) generates warnings to the clinician concerning the effects of the 18F contamination. A calibration processor (16) generates an estimated decay curve based on a time since the end of the proton bombardment which created the tracer and a priori information about the tracer. An activity meter (42) measures radiation emitted from a sample of the tracer and a dose calibrator (44) determines a decay curve from the measured radiation.

Abstract: The present invention is directed to a Gd2O2S:M fluorescent ceramic material with a very short afterglow, wherein M represents at least one element selected from the group Pr, Th, Yb, Dy, Sm and/or Ho and the Gd2O2S:M fluorescent ceramic material comprises further: europium of ?1 wt. ppm based on Gd2O2S, and cerium of ?0.1 wt. ppm to ?100 wt. ppm based on Gd2O2S, wherein the content of cerium is in excess of the content of europium with a ratio of europium to cerium of 1:10 to 1:150.

Abstract: The present invention relates to a fluorescent ceramic having the general formula Gd2O2S doped with M, whereby M represents at least one element selected form the group Ce, Pr, Eu, Tb, Yb, Dy, Sm and/or Ho, whereby said fluorescent ceramic comprises a single phase in its volume; to a method for manufacturing a fluorescent ceramic using single-axis hot pressing; a detector for detecting ionizing radiation and to a use of said detector for detecting ionizing radiation. The method for manufacture of a fluorescent ceramic material using a single-axis hot pressing, comprises the steps: a) selecting a pigment powder of Gd2O2S doped with M, and M represents at least one element selected from the group of Eu, Tb, Yb, Dy, Sm, Ho, Ce and/or Pr, whereby the grain size of said powder used for hot-pressing is of 1 ?m, and said hot-pressing is carried out at—a temperature of 1000° C. to 1400° C.; and/or—a pressure of 100 Mpa to 300 MPa; air annealing at a temperature of 700° C. to 1200° for a time period of 0.

Abstract: When performing image-guided biopsy of an anatomical structure in a patient, a target anatomical patient region containing biopsy target is imaged using both SPECT and XCT concurrently. 3D SPECT and XCT image data is fused to generate a fused 3D reference image (34) that is overlaid on 2D patient image(s) generated during the biopsy procedure to generate an overlay image. The overlay image also includes a planned path or trajectory for a biopsy instrument. The 2D patient images are generated using SPECT and/or XCT, and are updated periodically to show biopsy instrument position and progress.

Abstract: When performing nuclear (e.g., SPECT or PET) and CT scans on a patient, an imaging system (10) includes three or more carbon nanotube x-ray sources (20) are circumferentially spaced along an arc of a rotatable gantry (16) that spans a distance larger than a maximum cross-sectional dimension of a section of a patient (14) to be imaged. The x-ray sources are sequentially pulsed to emit x-rays for scanning a section of a patient (14) including a volume of interest (VOI) (13). Only one source (20) is in an ON state at a time to create a duty cycle, which reduces cooling time for the respective sources as well as radiation dose to the subject. X-rays traversing the patient (14) are received at a flat panel x-ray detector (22) that has a width smaller than the maximum cross-sectional dimesion, which further reduces the weight and size of the system (10).

Abstract: A radiation detector module for use in nuclear medical imagers employing radiation transmission or radiopharmaceuticals includes a rigid, optically opaque grid defined around a plurality of scintillator crystals. The grid defines a plurality of cells in which each scintillator crystal is completely disposed within in such a manner that an air layer exists between the scintillator crystal and the walls of the grid. A plurality of photoelectric detectors, each of which is associated with a corresponding scintillator crystal, are optically coupled to corresponding scintillator crystals by an optical coupling layer disposed within the cell.

Abstract: A detector arrangement providing imaging information at the edge of the scintillator is provided. The detector arrangement provides complete information and improved spatial resolution. SiPMs can be used in place of PMTs in order to provide the geometrical coverage of the scintillator and improved spatial resolution. With such detector arrangements, the spatial resolution can be under 2 mm. Furthermore, the overall thickness of the detector can be substantially reduced and depth of interaction resolution is also improved.

Abstract: A imaging system for acquiring an image of a subject comprising a gantry (810) having a plurality of detection modules (812). Each detection module comprising a radiation detector and a collimator adjacent a radiation receiving face of the detector. The collimator comprises a plurality of spaced slats and a body adjacent the slats which defines at least one elongated slit extending in an axial direction (824). The slit is arranged such that radiation (822) passes through the slit and between the slats to the detector. The body is opaque to the radiation. The detection modules have a common focus (820) and do not move during acquisition of the image.

Abstract: A nuclear medicine imaging system that includes a plurality of detectors arranged about an imaging region. A transmission source can be provided opposite the detectors and rotating about the imaging region to obtain different imaging angles. The nuclear imaging system provides for the ability to acquire high sensitivity transmission data with high emission data spatial resolution.

Abstract: The present invention relates to a fluorescent ceramic having the general formula Gd2O2S doped with M, whereby M represents at least one element selected form the group Ce, Pr, Eu, Tb, Yb, Dy, Sm and/or Ho, whereby said fluorescent ceramic comprises a single phase in its volume; to a method for manufacturing a fluorescent ceramic using single-axis hot pressing; a detector for detecting ionizing radiation and to a use of said detector for detecting ionizing radiation. The method for manufacture of a fluorescent ceramic material using a single-axis hot pressing, comprises the steps: a) selecting a pigment powder of Gd2O2S doped with M, and M represents at least one element selected from the group of Eu, Tb, Yb, Dy, Sm, Ho, Ce and/or Pr, whereby the grain size of said powder used for hot-pressing is of 1 ?m, and said hot-pressing is carried out at—a temperature of 1000° C. to 1400° C.; and/or—a pressure of 100 Mpa to 300 MPa; air annealing at a temperature of 700° C. to 1200° for a time period of 0.

Abstract: The present invention is directed to a Gd2O2S:M fluorescent ceramic material with a very short afterglow, wherein M represents at least one element selected from the group Pr, Th, Yb, Dy, Sm and/or Ho and the Gd2O2S:M fluorescent ceramic material comprises further: europium of ?1 wt. ppm based on Gd2O2S, and cerium of ?0.1 wt. ppm to ?100 wt. ppm based on Gd2O2S, wherein the content of cerium is in excess of the content of europium with a ratio of europium to cerium of 1:10 to 1:150.

Abstract: The invention relates to an X-ray detector with detector elements (1) arranged in a layer. The detector elements (1) contain a scintillator element (2) for the conversion of X-rays (X) into photons (v), a photodiode (5) for detection of the photons (v), and a processing circuit (4) for the processing of electric signals generated by the photodiode (5). In order to protect the electronics (4) from X-rays a shielding (3) of variable effective thickness (d1, d2) is disposed in front of the electronics (4). This shielding (3) can in particular be L-shaped. By reduction of the effective thickness of the shielding (3) to a necessary minimum the volume of the scintillator unit (2) can be maximized.

Abstract: The invention relates to an X-ray detector with detector elements (1) arranged in a layer. The detector elements (1) contain a scintillator element (2) for the conversion of X-rays (X) into photons (v), a photodiode (5) for detection of the photons (v), and a processing circuit (4) for the processing of electric signals generated by the photodiode (5). In order to protect the electronics (4) from X-rays a shielding (3) of variable effective thickness (d1, d2) is disposed in front of the electronics (4). This shielding (3) can in particular be L-shaped. By reduction of the effective thickness of the shielding (3) to a necessary minimum the volume of the scintillator unit (2) can be maximized.

Abstract: The invention relates to a detector element (1) for gamma radiation, which is particularly suitable for use in a PEF apparatus. The detector element (1) consists of two or more different conversion units (11, 12), which react to the absorption of a gamma quantum (y) with light emissions (?1, ?2) of different spectral composition. A photodetector arrangement (30) may therefore discriminate between the sites of origin of the light emissions by means of their spectral characteristics.