A radiation position detection method includes: a first step of calculating a first centroid position in an incident direction regarding positions where scintillation light is detected, on the basis of electrical signals; and a second step of specifying, on the basis of a first table showing first identification regions for identifying the plurality of segments, and the first centroid position, the segment that initially generates the scintillation light. The first identification region includes a first region, a second region, and a third region. In the second step, in a case where the first centroid position is located in the first region or the third region, the first segment is specified as the segment that initially generates the scintillation light, and in a case where the first centroid position is located in the second region, the second segment is specified as the segment that initially generates the scintillation light.

In a radiation position detection method, a scintillator that initially generates scintillation light is specified on the basis of a two-dimensional map showing regions for identifying a plurality of scintillators and the centroid position of positions where the scintillation light is generated. The regions shown in the two-dimensional map includes a first region corresponding to a first scintillator which is one of the plurality of scintillators, a second region corresponding to a second scintillator adjacent to the first scintillator among the plurality of scintillators, a third region that is located on the first region side and corresponds to the second scintillator, and a fourth region that is located on the second region side and corresponds to the first scintillator.

An imaging method and corresponding system (10) account for cascade gammas. Event data describing detected gamma rays emitted from a target volume of a subject are received. The detected gamma rays include cascade gammas emitted from a radionuclide within the target volume. Cascade and annihilation gamma emissions from the target volume and coincidence detection of the imaging system (10) are simulated using a Monte Carlo (MC) simulation technique to generate a cascade dataset comprised of annihilation coincidence events and cascade coincidence events. The event data is reconstructed into an image representation of the target volume with correction of cascade coincidence using the relationship between the annihilation coincidence events and the cascade coincidence events in the cascade data set.

The present disclosure relates to systems and methods for reconstructing a PET image. The systems may execute the methods to acquire PET data of a subject. The PET data may include position information of a plurality of coincident events. The plurality of coincident events may include scattering events and random events. The systems may execute the methods to select a portion of the PET data from the PET data based on the position information. The systems may execute the methods to reconstruct a first preliminary image of the subject based on the selected portion of the PET data, and project the first preliminary image. The systems may execute the methods to may determine, based on the PET data and the projection of the first preliminary image, preliminary correction data relating to the scattering events and the random events.

A method and system for acquiring a series of medical images includes a plurality of detectors configured to be arranged to acquire gamma rays emitted from a subject as a result of an advanced radionuclide administered to the subject and communicate signals corresponding to acquired gamma rays. A data processing system is configured to receive the signals from the plurality of detectors, determine double coincidence event dataset and a multiple coincidence event dataset, separate the multiple coincidence event dataset into at least one of a standard lines of response dataset and a nonstandard lines of response dataset, and apply a background correction to the double coincidence event dataset based on the non-standard lines of response dataset and/or the standard lines of response dataset to obtain a standard coincidence dataset.

A method of distinguishing effective pulses from test pulses in a scintillation detector that generates measurement light pulses includes providing a regularly-pulsed test light source that produces individual test light pulses having a time-dependent course of relative light intensity, which differs from a time-dependent course of relative light intensity of the measurement light pulses. The test light pulses are provided to a light detector for measurement of the test light pulses. The time-dependent courses of the relative light intensities of the test light pulses are analyzed. The measured pulses are separated into the test light pulses and the measurement light pulses according to the different time-dependent courses of the relative light intensities. The detector includes a scintillator, a light detector, a regularly-pulsed test light source that is adapted provide test light pulses to the light detector for measurement, and an electronic measuring circuit.

A photon detector for use in imaging, comprising a detector surface for detecting photons incident on the detector surface, the detector surface comprising at least one non-flat feature configured such that, during imaging, at least a portion of the photons are blocked from incidence upon at least a portion of the detector surface.

A method to generate an attenuation correction map to compensate imaging errors in emission tomography resulting from the presence of hardware parts inside the imaging volume of an emission tomograph. Components of 3-dimensional CAD models of the hardware parts to be compensated are converted into voxels on a predetermined grid and assigned a filling factor per voxel. Image data sets of each component are multiplied with respective attenuation coefficients and thereafter superimposed to form an attenuation correction map. Thereby, in a simple and automatable way a profoundly exact, mostly noise-free and exactly reproducible attenuation correction map for attenuation correction in an emission tomography device may be generated.

A method comprising: receiving a radiograph of at least a portion of a patient's body, wherein the radiograph is a digital grayscale image, and wherein each pixel of the grayscale image corresponds to a localized exposure index (EI) value; generating an HSL (Hue-Saturation-Lightness) image from the radiograph, wherein: a hue channel and a saturation channel of the HSL image are generated based on the localized EI values, a luminance channel of the HSL image is generated based on the intensity values of the pixels; and transforming the HSL image to an RGB image which conveys both the portion of the radiograph and the localized EI values.

A signal detected by a photomultiplier tube is pre-amplified and converted into a digital signal. A time average value of signal components, each of which has a voltage lower than a predetermined base threshold value, is calculated as a base voltage. A signal that has been subjected to base correction processing is subjected to threshold value processing and to base correction processing in a non-incident state in which light is not incident on the photomultiplier tube. An output signal thereof is subjected to dark current calculation processing; and a light emission signal amount is calculated by subtracting, from the signal component of the detection light obtained by the threshold value processing, a time average value of the signal components of the dark current. As the result, discriminating the dark current pulse from floor noises enhances the accuracy of the base voltage, and thus the accuracy of light detection.