Abstract: A system for generating registered diagnostic images (58, 62), such as nuclear and magnetic resonance (MR) images, of a subject includes a nuclear imaging device (10) for generating emission diagnostic images (58) and optionally also intermediate transmission or emission images (56). A second imaging device (12), such as an MR imaging device generates magnetic resonance diagnostic images (62) and optionally also intermediate images which are more readily registered with images from the nuclear imaging device than the diagnostic MR images. Processing for the images includes a preprocessing portion (64) for generating a transform for aligning common anatomical structures in images (56, 58, 60, 62) generated by the nuclear imaging device and the MR imaging device and a diagnostic image registration portion for applying the transform to bring the emission and magnetic resonance diagnostic images into registration (58, 62).

Abstract: A nuclear medicine imaging device includes a radiation camera (10) including a plurality of photo multiplier tubes (28). Each photo multiplier tube (28) is configured with an analog to digital converter (30) which converts a detected scintillation event (50) to sampled digital values. A storage device (66) is preloaded with an estimator function which can be derived from a calibration scintillation events. A processor (14) in communication with both the camera (10) and the storage device (66), detects an event and combines the digital values which are sampled together to arrive at a total area or energy of the scintillation event. Alternately, if a second pulse (52) is detected before the first scintillation event (50) has ended, the area combining (A1) of the first event is stopped and a pulse tail is estimated (A2) from the estimator functions stored. This estimated tail is then added to the combined data values taken until the time of pile-up.

Abstract: A scintillator crystal (22) for a diagnostic device (10) has a reflective surface which is dynamically adjustable. Radiation (42) from a diagnostic scan enters a detector (14a, 14b, 14c) and strikes the scintillator crystal (22). The scintillator crystal (22) converts the radiation into a plurality of scintillations or light photons (26) which travel in all directions. A plurality of photomultiplier tubes (30) are optically coupled to an optically transmissive plate (28) which is optically coupled to an exit surface of the scintillator crystal. The entrance surface of the scintillator crystal is polished and laminated with a liquid crystal layer (54). The liquid crystal layer has light dispersion and reflectivity properties which are dynamically adjustable in response to electrical (62) or chemical stimuli.

Abstract: The frequency divider of the present invention includes one or more regulated digital divider circuits, each of which is made up of a finite state machine such as a general purpose counter. The regulated digital divider circuits can be cascaded such that the frequency divider provides a high degree of precision within only a few stages, regardless of the division ratio. The frequency divider has an output duty cycle which is adjustable so as to provide a more useful output than existing frequency dividers. Moreover, the frequency divider can be implemented using simple logic circuitry and virtually any architecture.

Abstract: Pixel values f(m,n) of an image are reduced (A) by predicting each pixel value based on preceding pixel values and retaining the deviation e(m,n) between the actual and predicted values. The reduced values e(m,n) are serially fed to an input latch (20). A latched sizer (22) determines the larger of the number of bits of the value in the input latch and the largest previously received reduced value e(m,n). A comparator (42) compares a number of bits from the latched sizer with the number of bits per field indicated by a look-up table (44). Each time another reduced value e(m,n) is received, a state counter (46) indexes one state, i.e., increases the number of bit fields per output word and, when necessary causes the look-up table (44) to reduce the number of bits per field.

Abstract: A gantry (A) of a CT scanner system has an x-ray tube (10) and radiation detectors (14) which produce patient diagnostic data. An operator using a keyboard (20) or other manual controls operates the x-ray tube and other components of the gantry. The operator also causes a central processing unit (C) to process the diagnostic data with a selected algorithm to provide diagnostic information for display on a display (24). The same keyboard and displays are also utilized in routine service and repair processes. A system monitor (E) compares operating conditions sensed by sensors (50), such as operating temperatures and compares them with acceptable operating conditions. When the sensed conditions are unacceptable, a timer (60) is started and shuts down (68) gantry operation after a preselected duration. The operator can override (72) the timed shut down, but each such override is recorded (74) in permanent storage (32).