A position-signal processing method for flat panel gamma imaging probe includes a modeling phase and a use phase. In the modeling phase, a weight direction for an imaging detector is defined, position centers and weight ratios of the imaging detector in the weight direction are utilized to obtain a distribution graph of the weight ratios to the position centers, and curve fitting is performed upon the distribution graph to obtain a position estimation curve. In the use phase, the position estimation curve is utilized to derive a position estimation value of a probe trigger event in a 2D crystal diagram, a position value of the probe in the 2D crystal diagram with respect to the position estimation value of the probe trigger event is obtained, and a crystal code is located in a crystal code look-up table for the position value of the probe in the 2D crystal diagram.

The present invention provides an oxide-base scintillator single crystal having an extremely large energy of light emission, adoptable to X-ray CT and radioactive ray transmission inspection apparatus, and more specifically to provide a Pr-containing, garnet-type oxide single crystal, a Pr-containing perovskite-type oxide single crystal, and a Pr-containing silicate oxide single crystal allowing detection therefrom light emission supposedly ascribable to 5d-4f transition of Pr.

Among other things, one or more techniques and/or systems are described for presenting images derived from a photon counting imaging modality. Initially, a first image is derived by binning native projection data in a first manner to create first binned data and generating the first image using the first binned data. A region-of-interest within the object may be identified from the first image, and, based upon the identified region-of-interest, the native projection data may be rebinned in a second, different, manner to create second binned data. Because the second manner of binning the native projection data is different than the first manner, an image resulting from the second binned data may be different than the first image. Moreover, a user interface may be provided for assisting a user in selecting a region-of-interest and/or for specifying desired properties of the second image.

There is provided a detector component (40) for an X-ray or gamma ray detector, the detector component (40) comprising: a scintillating crystal having a plurality of scintillation crystal pixels (41), wherein each scintillating crystal pixel (41) is larger in one dimension than in the other two dimensions, and wherein each scintillating crystal pixel (41) has one or more light exit faces; and a photodetector (42) associated with at least one of the light exit faces of each scintillating crystal pixel (41), wherein a first and a second scintillating crystal pixel are arranged adjacent to one another, wherein a X-ray or gamma ray interaction with the first scintillating crystal pixel causes the generation of at least one photon, and optical cross talk of the at least one generated photon occurs between the first and the second scintillating crystal pixel, such that the X-ray or gamma ray interaction within the first scintillating crystal pixel is detected in use at the photodetector associated with a light exit face of the second scintillating crystal pixel.

Provided is a PET detector for reducing the number of silicon photomultipliers in use, which is characterized in that: the detector comprises layers respectively formed by a scintillation crystal array unit and a silicon photomultiplier (4) array unit, the scintillation crystal array unit and the silicon photomultiplier (4) array unit are rectangular cross sections in plan view, and the scintillation crystal array unit and the silicon photomultiplier (4) array unit have the same area of the rectangular cross sections in plan view; the scintillation crystal array unit consists of a plurality of scintillation crystal strips (1) parallel to each other, free of gaps and attached to each other on sides, the scintillation crystal strips (1) are all cuboids with uniform length, width and height; the silicon photomultiplier (4) array unit is an array assembly, which is formed by M silicon photomultiplier (4) arrays and has the rectangular cross section in plan view.

The disclosure relates to a scintillation pixel array, a radiation sensing apparatus, a scintillation apparatus, and methods of making a scintillation pixel array wherein scintillation pixels have beveled surfaces and a reflective material around the beveled surfaces. The embodiments described herein can reduce the amount of cross-talk between adjacent scintillation pixels.

A method and apparatus for generating crystal efficiency correction factors by performing a normalization calibration based on delayed data. The method and apparatus obtain delayed data from a scan of a patient using a Positron Emission Tomography (PET) scanner, generate a sinogram from the obtained delayed data, determine, using a processing circuit, mean fan and block line of response sensitivities from the generated sinogram, determine, using the processing circuit, mean detector efficiency based on the determined mean fan and block line of response sensitivities, determine, using the processing circuit, an individual crystal efficiency based on the determined mean fan and block line of response sensitivities and the mean detector efficiency for each module, and calculate the crystal efficiency correction factors based on the determined individual crystal efficiency of each module.

The invention relates to a hybrid medical PET-SPECT/MR imaging device comprising at least one scintillating crystal and at least one module for detecting radiation which contains at least one matrix of photodetectors and an electronics section, such that said module has a mechanical structure, the external, internal or both surfaces of which are divided into at least two sections, of which at least one is coated in graphene, and the rest in non-ferromagnetic conductive material, or all the sections are coated in graphene, and such that the coating forms a Faraday cage. The invention also relates to a shielding against radiofrequency for a medical imaging device, comprising a graphene coating, which is continuous or in bands, on all the faces of the mechanical structure of the detection module of the device, or a graphene coating, continuous or in bands, on at least one face, combined with a coating of non-ferromagnetic conductive materials on the remaining faces, and said shielding forming a Faraday cage.

A system and method for the measurement of radiation emitted from an in-vivo administered radioactive analyte. Gamma radiation sensors may be used to determine the proper or improper administration of a radioactive analyte, and identify patient administration factors that correlate with improper administration over a set of patients so as to identify administration risk factors to improve administration of radioactive analyte. In some cases, the system employs a sensor having a scintillation material to convert gamma radiation to visible light, which enables embodiments of the sensor to be ex vivo. A light detector converts the visible light to an electrical signal. This signal is amplified and is processed to measure the captured radiation. The sensor enables collection of sufficient data to support separate application to predictive models, background comparisons, or change analysis.

A detection apparatus for detecting high energy radiation, preferably for detecting gamma radiation, coming from a source of high energy radiation in a detection volume, e.g. from one or more particles emitting high energy radiation. The apparatus comprises at least one detection surface configured to convert incident high energy radiation into a detection signal, and a collimator system comprising at least three collimator slits. Each collimator slit is arranged to project high energy radiation coming from a respective slit field of view of said detection volume onto said detection surface. At least two of said collimator slits extend in non-parallel directions and the respective slit fields of view of said at least two non-parallel collimator slits and the slit field of view of any other of said at least three collimator slits overlap and define a common detection volume of the detection apparatus.