A dual mode radiation detector includes an x-ray detector layer configured to convert incident x-ray radiation into x-ray electrical data, where the x-ray detector forms an incident face of the dual mode radiation detector. The dual mode radiation detector further includes a collimator disposed below the x-ray detector layer, and a gamma photon detector layer disposed below the collimator to convert incident gamma photons into gamma photon electrical data.

A radiation detector can include a logic element configured to determine a depth of interaction based on a decay time corresponding to a radiation event and a constituent concentration profile of a radiation-sensing member. In another aspect, a method of detecting radiation can include determining a depth of interaction based on a decay time corresponding to a radiation event and a constituent concentration profile of a radiation-sensing member. The radiation detector and method can be useful in applications where depth of interaction is significant. The radiation-sensing member may include a variety of different materials, and is particularly well suited for alkali metal halides.

A system and method include execution of a first nuclear imaging scan to acquire first nuclear imaging scan data of a body; generation of a target image based on the first nuclear imaging scan data execute a second nuclear imaging scan to acquire second nuclear imaging scan data of the body association of each of a plurality of portions of the second nuclear imaging scan data with a respective one of a plurality of motion phases of the body, generation, for each of the plurality of motion phases of the body, of a binned image based on the portion of the second nuclear imaging scan data associated with the motion phase, performance of motion-correction on each of the plurality of binned images based on the target image to generate a plurality of motion-corrected binned images, and generation of an image based on the target image and the plurality of motion-corrected binned images.

Provided herein are compounds that are broad-spectrum protein kinase binding agents, detectable tracers comprising such compounds, and method of use thereof for the detection of protein kinases.

A Compton camera system and method for detecting gamma radiation, comprising a gamma radiation source, at least one fast scintillator plate P1 of which the rise time to peak light is less than 1 ns, having a thickness greater than or equal to 5 mm, equipped with an array of segmented photodetectors (5) and a dedicated fast-reading microelectronic means. The system is characterised in that it is capable of measuring the spatial and temporal coordinates (X, Y, Z, T) and energy E at at least two successive positions of a gamma photon when said photon undergoes Compton scattering at a first point A before being absorbed at a second point B, by recognising circles of non-scattered photons corresponding to each scintillation interaction. The system has a module for estimating a valid Compton event. The detection system has two scintillator plates P1 and P2.

Techniques for imaging radioactive emission in a target volume include collecting from each of multiple detectors in a Compton camera, within a coincidence time interval, location and deposited energy from an interaction associated with each high energy particle source event in a target volume, for N source events. A cone of possible locations for each source event is determined based on the locations and deposited energies collected. A SOE algorithm is initiated by selecting a random location on the cone and generating a histogram that indicates, a count of the selected locations that occur inside each voxel of the target volume. N solution locations for the N source events are determined after L iterations by updating the selected location on a corresponding cone based at least in part on values of the counts in the histogram excluding the current source event. A solution is presented on a display device.

The present disclosure relates to devices, systems and methods for determining a position of a photon gamma interaction in a PET detector. The PET detector may include a crystal array and a single-end read-out structure. The single-end read-out structure may include a photon-sensor array optically coupled with the crystal array. The crystal array may include a plurality of crystal elements arranged along a first direction and a second direction. The crystal elements may form a plurality of crystal groups along the first direction. The PET detector may further include a plurality of optical separators of the same or different lengths configured to control light transmission in the PET detector. The position of the photon gamma interaction in a crystal group may be determined based on output information of the photon-sensor array optically coupled with the crystal group.

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.

A detector module is provided that can be used as part of a time-of-flight positron emission tomography (TOF-PET) system. The detector module comprises a plurality of emitter elements, each emitter element including an emitter composed of a substance that produces scintillation light and/or Cherenkov radiation in response to gamma photons and, coupled to each of two opposing ends of the emitter, a plurality of photodetectors. The height or thickness of the emitters between their coupled photodetectors is less than 20 mm (e.g., 5-15 mm). The photomultipliers may be silicon photomultipliers or SiPMs that have surface areas less than approximately 9 mm.sup.2. Due to the quantity of photodetectors, their operating locations at both ends of each emitter, and the relative thinness of the emitters, the emitter elements and the detector module provide a timing resolution better (lower) than 100 ps full width at half maximum.