Methods and systems for detecting a three-dimensional position of a scintillation event converting a radiation into a light. For example, a system includes a crystal array including a plurality of crystal elements, a light sensor array including a plurality of light sensors, a first crystal pair of the plurality of crystal pairs corresponds to a first light sensor pair of the plurality of light sensor pairs; a second crystal pair of the plurality of crystal pairs corresponds to a second light sensor pair of the plurality of light sensor pairs; and a third crystal pair of the plurality of crystal pairs corresponds to the first light sensor pair and the second light sensor pair such that a scintillation event in the third crystal pair is detected by both the first light sensor pair and the second light sensor pair.

A magnet arrangement arranged radially around a sample volume generates a changing magnetic field B with a z-direction component A circuit board arrangement (6; 14) is arranged radially within the magnet arrangement and has electrical conductor tracks (7; 12) divided into conductor track sections (10), at least two adjoining ones of which form a structure section (11a, 11b) spanning an area (A1, A2). For each conductor track (7; 12), two structure sections (11a, 11b) respectively form a structure section pair (11), wherein the conductor tracks are arranged on the circuit board arrangement (6; 14) such that equal and opposite voltages and/or currents are induced by a change in the magnetic field B of the magnet arrangement in the two structure sections of each structure section pair. As a result, eddy currents and resultant interference in the circuit board and the components thereof are avoided or at least minimized.

A method for multidimensional direction measurement of gamma radiation in the far field by means of a group of several energy discriminating detectors synchronized with each other for detection of radiation can use unidirectional and bidirectional Compton scattering processes and lookup tables LUT.sup.SK, a defined functional value f(E1,E2), a list of defined detector pairs with an identification number i for defined detector pairs, and one or more frequency distributions Y for the acquisition of the measurement values. In some embodiments, the method can include setting up a detector system, acquiring measurement values, associating coincidence events with an Identification number, calculating a functional value, acquiring coincidence events in frequency distributions, and calculating one or more direction distributions from the frequency distributions.

Aspects of the subject disclosure may include, for example, a device comprising: a first micro-camera-element comprising a first sensor area and a first aperture element, the first aperture element having a first structural configuration, the first aperture element and the first sensor area being disposed relative to each other in order to cooperate in obtaining first imaging data having first characteristics, and the first characteristics comprising first imaging resolution and first angular coverage; a second micro-camera-element comprising a second sensor area and a second aperture element, the second aperture element having a second structural configuration, the second aperture element and the second sensor area being disposed relative to each other in order to cooperate in obtaining second imaging data having second characteristics, the second characteristics comprising second imaging resolution and second angular coverage, and the first imaging resolution differing from the second imaging resolution, the first angular coverage differing from the second angular coverage, or any combination thereof. Additional embodiments are disclosed.

A radiation diagnostic device according to an aspect of the present invention includes a first detector, a second detector, and processing circuitry. The first detector detects Cherenkov light that is generated when radiation passes. The second detector is disposed to be opposed to the first detector on a side distant from a generation source of the radiation, and detects energy information of the radiation. The processing circuitry specifies Compton scattering events detected by the second detector, and determines an event corresponding to an incident channel among the specified Compton scattering events based on a detection result obtained by the first detector.

A PET imaging device for observing a brain includes a hollow three-dimensional structure with a shape capable of housing a head. The PET imaging device comprising multiple independent gamma ray detection modules that together form a structure capable of surrounding the head, said detection modules comprise continuous scintillation crystal blocks, wherein “continuous” means that the crystal blocks can be continuous in one or in two directions, each of the continuous scintillation crystal blocks has a polygonal main cross-section, and said structure is an elongated structure having a major axis in a direction corresponding to the front-nape direction and a shorter axis in a direction corresponding to a straight line joining ears on the head. The continuous scintillation crystal blocks are positioned adjacent to fit laterally in an exact manner with each other throughout their entire thickness, building a mosaic, without gaps between adjacent crystal blocks and without overlapping each other.

According to one embodiment, medical image diagnostic apparatus includes a bed, a display, and processing circuitry. The bed movably supports a top plate. The display displays a setting window for setting an acquisition time of PET event data for each acquisition area. The processing circuitry sets an acquisition time for each acquisition area in response to a setting instruction of the acquisition time for each acquisition area. The acquisition area includes a unit acquisition area or a plurality of unit acquisition areas which overlap with each other with variable overlap ratio. The unit acquisition area corresponds to a coverage of a gamma ray detector. The processing circuitry adjusts the overlap ratio of at least one of two neighboring acquisition areas so that the boundary of the neighboring acquisition areas is set to a position designated by a user.

When designing detector arrays for diagnostic imaging devices, such as PET or SPECT devices, a virtual detector, or pixel, combines scintillator crystals with photodetectors in ratios that deviate from the conventional 1:1 ratio. For instance, multiple photodetectors can be glued to a single crystal to create a virtual pixel which can be software-based or hardware-based. Light energy and time stamp information for a gamma ray hit on the crystal can be calculated using a virtualizer processor or using a trigger line network and time-to-digital converter logic. Additionally or alternatively, multiple crystals can be associated with each of a plurality of photodetectors. A gamma ray hit on a specific crystal is then determined by a table lookup of adjacent photodetectors that register equal light intensities, and the crystal common to such photodetectors is identified as the location of the hit.

To capture more emitted photons with a Compton camera, the scatter detector is tilted (non-orthogonal angle) relative to a radial from the isocenter of the imaging system. The tilt creates a greater volume for scatter interaction. To capture more scatter photons, the catcher detector is non-planar, such as a multi-faced detector at least partially surrounding a volume behind the scatter detector. The tilted scatter detector alone, the non-planar catcher detector alone, or the tilted scatter detector and the non-planar catcher detector are used in the Compton camera.

A collimator for a detector is disclosed. The collimator comprises: a bottom plate provided with imaging through holes distributed in an array, each of the imaging through holes comprising a first hole segment and a second hole segment, the transverse size of the first hole segment gradually decreasing in a direction from a free end to the second hole segment, and the transverse size of the second hole segment gradually decreasing in a direction from the free end to the first hole segment; a shielding case formed on the bottom plate; and a top plate disposed in the shielding case and closing at least a part of an opening of the shielding case, the top plate being provided with shielding through holes distributed in an array, and the imaging through holes being in one-to-one correspondence with the shielding through holes.