The present invention provides a rare-earth halide scintillating material and application thereof. The rare-earth halide scintillating material has a chemical formula of RE.sub.aCe.sub.bX.sub.3, wherein RE is a rare-earth element La, Gd, Lu or Y, X is one or two of halogens Cl, Br and I, 0≤a≤1.1, 0.01≤b≤1.1, and 1.0001≤a+b≤1.2. By taking a +2 valent rare-earth halide having the same composition as a dopant to replace a heterogeneous alkaline earth metal halide in the prior art for doping, the rare-earth halide scintillating material is relatively short of a halogen ion. The apparent valence state of a rare-earth ion is between +2 and +3. The rare-earth halide scintillating material belongs to non-stoichiometric compounds, but still retains a crystal structure of an original stoichiometric compound, and has more excellent energy resolution and energy response linearity than the stoichiometric compound.

Disclosed is a general PET device (1) with a gradually narrowed head, the device comprising a body (2), a head (3) and a top (4) closely arranged in sequence, wherein the body (2) is composed of a plurality of body module rings (21); the head (3) is composed of N head module rings (31), with N being a natural number and being at least two; the top (4) is composed of a plurality of top PET detection modules (41); each of the body module rings (21) is composed of several body PET detection modules (22) evenly distributed in a circumferential direction thereof, and all the body module rings (21) are closely arranged in an axial direction to form the body (2); in the N head module rings (31), the rings sequentially decreases in size, and are closely arranged in the axial direction in a sequence from the first head module ring (31) to the Nth head module ring (31); and the detection surfaces of the plurality of top PET detection modules (41) are located in the same plane, and all the detection surfaces face the head (3) or the body (2).

Described here are systems and methods for optimization techniques for automatically selecting x-ray beam spectra, energy threshold, energy bin settings, and other imaging technique parameters for photon-counting detector computed tomography (“PCCT”). The techniques described here are generally based on subject or object size, material of interest, and location of the target material. Advantageously, the optimizations can be integrated with different PCCT systems to automatically select optimal imaging technique parameters before scanning a particular subject or object.

The present disclosure relates to a PET detector and a PET frame. The PET detector may include a plurality of detector modules and a plurality of installing modules configured to install the plurality of detector modules. The plurality of installing modules may be coupled together to form a detector ring. The PET frame may include a detector stabilizing cylinder configured to stabilize a detector and a fixing support configured to support the detector stabilizing cylinder. The detector stabilizing cylinder may be rotatably fixed on the fixing support.

The present invention relates to a radiation detector (100) comprising: i) a substrate (110); ii) a sensor, which is coupled to the substrate, the sensor comprising a first array (120) of sensor pixels, a second array (130) of signal read-out elements, and an electronic circuitry which is configured to provide image data based on signals received from the signal read-out elements; iii) a transducer, which is coupled to the substrate and to the sensor, the transducer comprising a third array (140) of subpixels, wherein at least two subpixels are assigned to one sensor pixel; wherein the second array of signal read-out elements and the third array of subpixels correspond to each other; wherein each of the subpixels comprises a radiation conversion material.

Uptake of hypoxia-sensitive PET tracers is dependent on tissue transport properties, specifically, distribution volume. Variability in tissue transport properties reduces the sensitivity of static PET imaging to hypoxia. When tissue transport (v.sub.d) effects are substantial, correlations between the two methods of determining hypoxic fractions are greatly reduced—that is, trapping rates k.sub.3 are only modestly correlated with tumour-to-blood ratio (TBR). In other words, the usefulness of dynamic- and static-PET based hypoxia surrogates, trapping rate k.sub.3 and TBR, in determining hypoxic fractions is reduced in regions where diffusive equilibrium is achieved slowly. A process is provided for quantifying hypoxic fractions using a novel biomarker for hypoxia, hypoxia-sensitive tracer binding rate k.sub.b, based on PET imaging data. The same formalism can be applied to model the kinetics of non-binding CT and MT contrast agents, giving histopathological information about the imaged tissue.

A method for calibrating defective channels of a CT device involves in a step S10, acquiring original data collected by the CT device; in a step S20, capturing to-be-recovered areas from the original data, wherein the to-be-recovered areas contain the defective channels of the CT device; in a step S30, inputting data of the to-be-recovered areas to a neural network for training so as to generate training results; and in a step S40, using the training results to repair the to-be-recovered areas. The method eliminates effects of artifacts caused by defective channels on image reconstruction.

Examples of the present disclosure relate to a particle beam dose profile measurement apparatus comprising a particle detector stack comprising a plurality of scintillator layers. Each scintillator layer of the detector stack is disposed along an axis of the apparatus such that the axis projects through each layer. Each scintillator layer is configured to produce scintillation light indicative of an energy deposition, in that scintillator, of a particle beam incident upon the detector stack along said axis. The apparatus comprises readout circuitry configured to measure the scintillation light of each scintillator layer; and dose profile determination circuitry configured to determine a dose profile of said particle beam within the detector stack. Said determining is based on the measured scintillation light of each scintillator layer, and a quenching correction.

A list mode image reconstruction method includes a step of dividing list mode data into a plurality of subsets and a step of acquiring a subset balance coefficient based on the number of events in the plurality of subsets.

A detector module is provided. The detector module may include a plurality of detector sub-modules. Each of the plurality of detector sub-modules may include a detection layer, at least one data acquisition circuitry, a frame for supporting the detection layer, and a positioning element for assembling the plurality of detector sub-modules. The frame may include a plurality of heat transfer fins that are thermally connected with the at least one data acquisition circuitry for dissipating heat produced by the at least one data acquisition circuitry.