An X-ray detector integral with an automatic exposure control (AEC) device can include an X-ray detection part configured to detect X-rays irradiated from an X-ray source and generate X-ray image data; and an automatic exposure detection board located below the X-ray detection part and configured to generate an X-ray sensing signal for automatic exposure control based on residual X-rays which have passed by or through the X-ray detection part.

A scintillation crystal can include a rare earth silicate, an activator, and a Group 2 co-dopant. In an embodiment, the Group 2 co-dopant concentration may not exceed 200 ppm atomic in the crystal or 0.25 at % in the melt before the crystal is formed. The ratio of the Group 2 concentration/activator atomic concentration can be in a range of 0.4 to 2.5. In another embodiment, the scintillation crystal may have a decay time no greater than 40 ns, and in another embodiment, have the same or higher light output than another crystal having the same composition except without the Group 2 co-dopant. In a further embodiment, a boule can be grown to a diameter of at least 75 mm and have no spiral or very low spiral and no cracks. The scintillation crystal can be used in a radiation detection apparatus and be coupled to a photosensor.

A ray detector substrate has detection regions and includes a substrate, a first interdigital electrode and a second interdigital electrode disposed on a side of the substrate and located in each detection region, a first scintillator layer disposed on a side of the first interdigital electrode and the second interdigital electrode away from the substrate, and a second scintillator layer disposed on a side of first scintillator layer away from the substrate. The second scintillator layer is configured to convert part of rays incident onto the detection region into visible light, and transmit another part of the rays, so that the another part of the rays is incident onto the first scintillator layer through the second scintillator layer. The first scintillator layer is configured to convert the visible light converted by the second scintillator layer and the another part of the rays through the second scintillator layer into photocurrent.

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.

The present invention relates to a rare earth halide scintillating material. The material has a general chemical formula La.sub.1-xCe.sub.xBr.sub.3+y, wherein 0.001x1, and 0.0001y0.1. The rare earth halide scintillating material involved in the present invention has excellent scintillation properties of high light output, high energy resolution, and fast decay.

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).

The invention relates to a solution for determining events related to photons and charged particles useful in therapies that use methodologies related to hadron therapy. In one aspect of the invention, it relates to a device having a sandwich-type structure of photon-detecting panels (1) and charged particle-detecting panels (2), which can be suitably associated with respective sensors. Also included is a method for detecting photons and charged particles that uses the aforementioned device. Lastly, a specific use of the object of the invention in hadron therapy is described.

An object of the present invention is to provide a scintillator having a high radiation stopping power, and having a shorter fluorescence decay time compared to conventional scintillators. The above object is achieved by setting the composition of a scintillator to a composition represented by General Formula (1).

Q.sub.xM.sub.yO.sub.3z  (1)

(wherein in General Formula (1), Q includes at least two or more divalent metallic elements; M includes at least Hf; and x, y, and z independently satisfy 0.5≤x≤1.5, 0.5≤y≤1.5, and 0.7≤z≤1.5, respectively).

A method of tailoring the properties of garnet-type scintillators to meet the particular needs of different applications is described. More particularly, codoping scintillators, such as Gd.sub.3Ga.sub.3Al.sub.2O.sub.12, Gd.sub.3Ga.sub.2Al.sub.3O.sub.12, or other rare earth gallium aluminum garnets, with different ions can modify the scintillation light yield, decay time, rise time, energy resolution, proportionality, and/or sensitivity to light exposure. Also provided are the codoped garnet-type scintillators themselves, radiation detectors and related devices comprising the codoped garnet-type scintillators, and methods of using the radiation detectors to detect gamma rays, X-rays, cosmic rays, and particles having an energy of 1 keV or greater.

A detector is for electromagnetic radiation. In an embodiment, the detector includes a first, pixelated electrode layer, a second electrode, and a first layer including at least one first perovskite, located between the first, pixelated electrode layer and the second electrode. An embodiment further relates to a method for manufacturing a corresponding detector.