This disclosure describes an imaging radiation detection module with novel configuration of the scintillator sensor allowing for simultaneous optimization of the two key parameters: detection efficiency and spatial resolution, that typically cannot be achieved. The disclosed device is also improving response uniformity across the whole detector module, and especially in the edge regions. This is achieved by constructing the scintillation modules as hybrid structures with continuous (also referred to as monolithic) scintillator plate(s) and pixellated scintillator array(s) that are optically coupled to each other and to the photodetector. There are two basic embodiments of the novel hybrid structure: (1) the monolithic scintillator plate is at the entrance for the incoming radiation, preferably gamma rays, and the pixellated array placed behind the plate, all in optical contact with the photodetector, (2) the order of the scintillator components is reversed with the pixellated scintillation plate placed in front of the monolithic plate.

Provided is are a particle detection device and method of fabrication thereof. The particle detection device includes a scintillator array that includes a plurality of scintillator crystals; a plurality of detectors provided on a bottom end of the scintillator array; and a plurality of prismatoids provided on a top end of the scintillator array. Prismatoids of the plurality of prismatoids are configured to redirect particles between top ends of crystals of the scintillator array. Bottom ends of a first group of crystals of the scintillator array are configured to direct particles to a first detector of the plurality of detectors and bottom ends of a second group of crystals of the scintillator array are configured to direct particles to a second detector substantially adjacent to the first detector.

A scintillation crystal can include a cesium halide that is co-doped with thallium and another element. In an embodiment, the scintillation crystal can include CsX:Tl, Me, where X represents a halogen, and Me represents a dopant selected from the group consisting of chromium (Cr), zirconium (Zr), cobalt (Co), manganese (Mn), cadmium (Cd), dysprosium (Dy), thulium (Tm), tantalum (Ta), and erbium (Er), the dopant concentration of the element selected from the group consisting of chromium (Cr), zirconium (Zr), cobalt (Co), manganese (Mn), cadmium (Cd), dysprosium (Dy), thulium (Tm), tantalum (Ta), and erbium (Er) in the scintillation crystal is in a range of 1×10.sup.−7 mol % to 0.5 mol %. In a particular embodiment, the scintillation crystal may have a cesium iodide host material, a first dopant including a thallium cation, and a second dopant including a cation.

The following relates to noise filtering in nuclear imaging systems. In one aspect, a fully automatic noise filtering system is provided in a nuclear imaging device. In some embodiments, a filter parameter selection engine is applied to an image environment of a medical image to calculate an image filter configuration for the medical image wherein the image environment includes values for one or more of an imaging subject of the medical image, an imaging device used to acquire the medical image, and a medical context of the medical image.

A nuclear detector, comprises a scintillation crystal array including a plurality of scintillation crystal bars of the same size arranged closely and in sequence, a light guide, and a photodetector array including a plurality of photodetectors arranged in sequence. The photodetectors have a cross-sectional area greater than that of the scintillation crystal bars, and the light guide includes a top surface coupled to the scintillation crystal array, an opposed bottom surface coupled to the photodetector array and a side surface. The light guide has a thickness in a range of 0.1 mm to 40 mm. The light guide further includes a slit adjacent to an edge of the light guide, and the slit is configured to extend from the top surface toward the bottom surface of the light guide and the slit has a depth in a range of 0.1 to 0.5 times the thickness of the light guide.

For SPECT-based internal dose estimation, a portable detector is used to sample activity. The portable detector may selectively use far-field or near-field imaging for a SPECT scan. A camera and/or gyroscope assist in determining emission location and/or aligning activities from the different times. The time-activity curve or another dose is estimated using activities from different times where the activity for at least one time is from the portable detector, which may allow for more frequent sampling of activity and more accurate dose estimation.

The invention is an imaging device comprising detector and collimator element (144) applied e.g. in a SPECT. In the imaging device according to the invention the collimator element comprises—one or more first pinholes (146a, 148a) being focussed on a central field of view (141), the one or more first pinholes (146a, 148a) being adapted for projecting the central field of view (141) on one or more respective first imaging regions (52) being non-overlapping with any other imaging regions;—one or more second pinholes (148b) being focussed on a central field of view (141), the one or more second pinholes (148b) being adapted for projecting the central field of view (141) on one or more respective second imaging regions (56);—one or more second pinholes (148c) being focussed on a primary field of view (142) comprising the central field of view (141), the one or more third pinholes (148c) being adapted for projecting the primary field of view (142) on one or more respective third imaging regions (58) overlapping with at least one second imaging region (56). The invention is furthermore a tomographic apparatus (e.g. a SPECT) comprising the imaging device. (FIG. 13).

One embodiment provides a gamma camera system, including: a stand, a rotatable gantry supported by the stand, and a transformable gamma camera connected by mechanical supports to the rotatable gantry and comprising groups of tiled arrays of gamma detectors and a collimator for each group of tiled arrays of gamma detectors; the transformable gamma camera being configured to subdivide into a plurality of subdivided gamma cameras, each of the subdivided gamma cameras having at least one of the groups of tiled arrays of gamma detectors and corresponding collimator, wherein the subdivision into a plurality of subdivided gamma cameras facilitates contouring with a region of interest for a spatial resolution. Other embodiments are described and claimed.

Among other things, one or more techniques and/or systems are described for setting a sampling frequency for a radiation imaging system. The radiation imaging system comprises a rotating gantry configured to rotate a radiation source and a detector array about an object to generate an image(s) of the object. A data acquisition system is configured to sample the detector array as views. One or more flag structures are arranged according to a partial arc segment (e.g., a structure less than a full 360 degree circle). One or more sensors are disposed on one of the rotating gantry or a stationary support about which the rotating gantry rotates. When a sensor encounters a flag structure, a current rotational speed of the rotating gantry is determined. A clock frequency is updated based upon the current rotational speed to establish a sampling frequency for the data acquisition system for sampling the detector array.

Provided area device for detecting sub-atomic particles and method of fabrication thereof. The device includes a plurality of scintillators, a detector provided on a first end of the plurality of scintillators and a prismatoid provided on a second end of the plurality of scintillators. The prismatoid redirects light between adjacent scintillators of the plurality of scintillators.