During calibration of a SPECT system, system-specific sensitivities and cross-calibration factors for multiple isotopes for correcting for dose are determined for various combinations of options, including the option of which specific well counter with which to measure the dose. The options may include selected energy windows for isotopes with multiple energy windows. This arrangement allows for custom-specified isotopes not included in standard listings. For use with a particular patient, the cross-calibration factor for the well counter used to measure the dosage for the patient is accessed and used for dose correction. More accurate quantitative functional information may result from the corrected dose. The cross-calibration may be more easily implemented despite the options using the sensitivities and cross-calibrations provided for various combinations.

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 for photosensor signal processing includes carrying out, by measuring a combination of readout channels of a direction e with linearly increasing and linearly decreasing signal strength, a linear coding in at least one e-direction. The linearly increasing and linearly decreasing signal strengths of readout channels of the direction e, which are respectively used for the linear coding, are multiplied by each other. The linear coding satisfies the following edge condition: Q.sub.1(e)=c.sub.1.Math.e.sup.c2+c.sub.3, Q.sub.2(e)=c.sub.4.Math.e.sup.c5+c.sub.6, c.sub.1=const.(0, ), c.sub.4=const.(, 0), c.sub.3, c.sub.6=const.(, ), and 0.5<c.sub.2; c.sub.5<1.5. Q1 denotes the charge of the output channel signal strengths increasing via the e-position, and Q2 denotes the charge of the output channel signal strengths decreasing via the e-position and the coding direction.

Described is a scintigraphic measurement device with extended area, including a measurement structure having a matrix of scintillation crystals and an optoelectronic network for converting photons into electrical signals; a collimator with collimation channels; an electronic processing unit applied to the measurement structure processing the electrical signals generated by the measurement structure. The optoelectronic network has a matrix of optoelectronic conversion modules interconnected according to a two-dimensional distribution to cover the entire measurement area, each optoelectronic conversion module including a two-dimensional matrix of individual elements Multi Pixel Photon Counter or individual Silicon PhotoMultiplier elements electrically interconnected, and wherein the optoelectronic conversion modules are electrically connected to each other along rows and columns by channels for each row or column and the electronic processing unit is connected to the optoelectronic network for measuring a total electric current of each channel delivered by the optoelectronic conversion modules positioned on the channel.

An X-ray detector (100) includes a pixelated array (110) of X-ray detector elements (130.sub.i,j) configured to determine detection times of received X-ray quanta from detection events representing the received X-ray quanta; and a processor (120) estimates an amount of scattered X-ray quanta received by the X-ray detector elements (130.sub.i,j) based on a count of pairs of detection events detected within a predetermined time interval of each other by adjacent X-ray detector elements (130.sub.i,j, 130.sub.i,j(a . . . h)) in the pixelated array (110).

A nuclear medicine diagnosis apparatus according to an embodiment includes processing circuitry. The processing circuitry is configured: to obtain first photon number information detected by a first detector and second photon number information detected by a second detector different from the first detector; to calculate a first light emission probability model corresponding to the first detector on the basis of the first photon number information and a second light emission probability model corresponding to the second detector on the basis of the second photon number information; and to specify a probability distribution model related to a detection time difference along a Line Of Response (LOR) defined by the first detector and the second detector, on the basis of the first light emission probability model and the second light emission probability model.

A nuclear medicine diagnostic device according to an embodiment includes processing circuitry. The processing circuitry obtains first photon-number information detected by a first detector; calculates, based on the first photon-number information, a first light emission probability model corresponding to the first detector; identifies, based on the first light emission probability model, a first timing at which the detection probability becomes equal to or greater than a predetermined threshold value; measures the detection timing of an event detected by the first detector; and corrects the detection timing based on the first timing.

A method of operation of a scintillator detector includes a scintillator and a photodetector is described, together with a device embodying the method. The method includes the steps of: periodically producing a light pulse; impinging at least some of the light from a successive plurality of such light pulses onto a light-receptive part of the photodetector; measuring the electrical response of the photodetector; processing the electrical response of the photodetector to determine a pulse height and a variance of pulse height; numerically processing the pulse height and variance of pulse height so determined to obtain at least a first data item characteristic of the response of the photodetector.

A partial-ring PET device, in which some of coincidence radiation detectors to be arranged in a ring shape around a field of view for detecting lines of response of annihilation radiations are missing, is compensated for a drop in image quality due to the missing of the coincidence radiation detectors by including single gamma-ray radiation detectors for detecting at least either one of the annihilation radiations as a single gamma-ray. This can reduce missing of projection angles and reduce artifacts in PET images.

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.