Abstract: A diagnostic imaging device includes a signal processing circuit (22) processes signals from a detector array (16) which detects radiation from an imaging region (20). The hit signals are indicative of a corresponding detector (18) being hit by a radiation photon. The signal processing circuit (22) includes a plurality of input channels (321, 322, 323, 324), each input channel receiving hit signals from a corresponding detector element (18) such that each input channel (321, 322, 323, 324) corresponds to a location at which each hit signal is received. A plurality of integrators (42) integrate signals from the input channels (32) to determine an energy value associated with each radiation hit. A plurality of analog-to-digital converters (441, 442, 443, 444) convert the integrated energy value into a digital energy value. A plurality of time to digital converters (40) receive the hit signals and generate a digital time stamp.

Abstract: In a combined system, a magnetic resonance (MR) scanner includes a magnet (10, 110) configured to generate a static magnetic field (B0) at least in a MR examination region (12) from which MR data are acquired. Radiation detectors (40, 41, 140) are configured to detect gamma rays generated by positron-electron annihilation events in a positron emission tomography (PET) examination region (70). The radiation 5 detectors include electron multiplier elements (60, 160) having a direction of electron acceleration (ae) arranged substantially parallel or anti-parallel with the static magnetic field (B0). In some embodiments, the magnet is an open magnet having first and second spaced apart magnet pole pieces (14, 15) disposed on opposite sides of a magnetic 10 resonance examination region, and the radiation detectors include first and second arrays (40, 41) of radiation detectors disposed with the first and second spaced apart magnet pole pieces.

Abstract: In nuclear imaging, solid state photo multipliers (48) are replacing traditional photomultiplier tubes. One current problem with solid state photomultipliers, is that they are difficult to manufacture in the size in which a typical scintillator is manufactured. Resultantly, the photomultipliers have a smaller light receiving face (50) than a light emitting face (46) of the scintillators (44). The present application contemplates inserting a reflective material (52) between the solid state photomultipliers (48). Instead of being wasted, light that initially misses the photomultiplier (48) is reflected back by the reflective material (52) and eventually back to the radiation receiving face (50) of the photomultiplier (48).

Abstract: A generally cylindrical set of coil windings (10, 30, 80) includes primary coil windings (12, 32, 82) and shield coil windings (14, 34, 84) at a larger radial position than the primary coil windings, and an arcuate or annular central gap (16, 36, 86) that is free of coil windings, has an axial extent (W) of at least ten centimeters, and spans at least a 180° angular interval. Connecting conductors (24, 44, 94) disposed at each edge of the central gap electrically connect selected primary and secondary coil windings. In a scanner setting, a main magnet (62, 64) is disposed outside of the generally cylindrical set of coil windings. In a hybrid scanner setting, an annular ring of positron emission tomography (PET) detectors (66) is disposed in the central gap of the generally cylindrical set of coil windings.

Abstract: A positron emission tomography apparatus (100) includes a plurality of radiation sensitive detector systems (106) and selective trigger systems (120). The selective trigger systems identify detector signals resulting from detected gamma radiation (310) while disregarding spurious detector signals (310). In one implementation, the apparatus (100) includes a time to digital converter which decomposes a measurement time interval (Tmax) according to a binary hierarchical decomposition of level H, where H is an integer greater than equal to one.

Abstract: The invention relates to a scintillation layer (20) for a PET-detector. The scintillation layer (20) consists of a plurality of scintillation elements (21) that are joined together in a practically gapless way and that are oriented towards the centre of curvature (24). Depending on the form of the scintillation layer (20), the scintillation elements (21) may have for example the form of a truncated wedge or pyramid.

Abstract: In a system for driving inertia-prone picture-reproducing devices, in particular liquid-crystal displays, in which a correcting value that depends on changes in the video signals from frame to frame is added to incoming video signals to compensate for the inertial effects and in which the corrected video signals are passed to the picture-reproducing device to form the correcting value, a model of the picture-reproducing device is provided that has a state variable as an output variable, the video signals as a first input variable and the state variable from a preceding frame as a second input variable. Furthermore, to derive the correcting value, a function having the incoming video signals and the state variable of the preceding variable as input variables and the corrected video signals as an output variable.

Abstract: In a method and arrangement for correcting an arrangement for driving imagereproducing means subject to inertia, and particularly liquid crystal displays, wherein a stored correcting variable is added to infed video signals to compensate for the effects of inertia, which correcting variable depends on changes in the video signals from frame to frame, and wherein the corrected video signals are conveyed to the image-reproducing means, provision is made for a test pattern that contains signal jumps that occur from frame to frame to be generated, for the signal jumps to vary in respect of their sign, their size and their position in the amplitude range of the video signals, for the test video signals to be shown on the imagereproducing means at least in a part that is covered by at least one opto-electrical sensor, and for correcting parameters to be derived from the signals generated by the at least one optoelectrical sensor while taking account of the totality of the signals generated by the at least one opto-

Abstract: The invention relates to an imaging (X-ray) system for observing the motion of an object in the vascular system of a body volume (10). An X-ray apparatus (3) in this system generates two-dimensional projection images (4) of the body volume (10). In a module (5) the position of the tip of the object is determined from the projection images and this position is associated, in a further module (2), with a previously acquired three-dimensional representation (1) of the vascular system. The module (2) then calculates optimum imaging parameters which involve notably a planar projection of the tip of the object and a minimum projection window. These parameters are subsequently set on the X-ray apparatus (3) so as to serve as a basis for the next two-dimensional image (4).

Abstract: An imaging ultrasound system is provided with an ultrasound transducer and an image processing unit for the acquisition of a three-dimensional ultrasound image of the body of a patient, and a catheter for carrying out a therapeutic or diagnostic intervention in the body of the patient. The catheter accommodates, in addition to the customary instruments necessary to carry out its task, three ultrasound receivers that are mounted at a distance from one another on the tip of the catheter and are capable of detecting the arrival of scan signals of the ultrasound transducer. The distance between the ultrasound transducer and the receivers can be calculated from the transit time of the scan signals. The receivers can thus be localized in space. Localization enables notably the selection of, for example, the plane from the three-dimensional ultrasound data that contains all three receivers of the catheter.

Abstract: The invention relates to an imaging ultrasound system that is provided with an ultrasound transducer (1) and an image processing unit (2) for the acquisition of a three-dimensional ultrasound image of the body of a patient (11), as well as with a catheter (9) for carrying out a therapeutic or diagnostic intervention in the body of the patient. The catheter (9) accommodates, in addition to the customary instruments necessary to carry out its task, three ultrasound receivers (10a to c) that are mounted at a distance from one another on the tip of the catheter and are capable of detecting the arrival of scan signals of the ultrasound transducer (1). The distance between the ultrasound transducer (1) and the receivers (10a to c) can be calculated from the transit time of the scan signals. The receivers (10a to c) can thus be localized in space; this enables notably the selection of, for example, the plane from the three-dimensional ultrasound data that contains all three receivers (10a to c) of the catheter.