Time-to-digital converter system including: an event detector configured for detecting an event and generating an event detection signal upon detection of the event; and a time-to-digital converter coupled or connectable to the event detector and including a fine resolution part configured for counting fine time intervals, organized such that the fine resolution part is activated in response to the event detection signal and deactivated in response to a reference clock. 3D imager including an array of pixels, with in each pixel such a time-to-digital converter system, and further including a reference clock generator.

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.

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.

An online real-time correction method and system for a positron emission tomography (PET) detector. The method includes: acquiring a drifted channel number of a peak position of a full-energy peak in a drifted energy spectrum after a gain value of a PET detector system has changed and a ratio of a currently accumulated energy of each signal channel to a current total accumulated energy of all signal channels; substituting the above parameters, an initial channel number of the peak position of the full-energy peak in an initial energy spectrum and a ratio of an initially accumulated energy of each signal channel to a total initially accumulated energy of all of the signal channels in the PET detector system into a gain adjustment ratio calculation formula to calculate a gain adjustment ratio; and adjusting, according to the gain adjustment ratio, a gain value of the PET detector system.

A nuclear medicine diagnostic apparatus according to an embodiment includes a scintillator configured to be formed of a single crystal and convert a gamma ray into light; a plurality of photodetectors configured to be arranged on different faces or tangents of the scintillator and each of which is configured to output an electric signal in response to incidence of the light resulting from the converting by the scintillator; storage circuitry configured to store, in advance, correspondence information in which each position in the scintillator is associated with a first intensity distribution indicating intensities of the electric signals that are output by the respective photodetectors; and specifying circuitry configured to specify a conversion position in which the gamma ray that is emitted from the subject is converted into the light in the scintillator by using the correspondence information and a second intensity distribution indicating the intensities of the electric signals.

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.

A channel multiplexing method for reading out a detector signal is provided, including steps: grouping L detectors to form a first source signal and a second source signal; respectively introducing L detector signals into a first signal transmission line including two readout channels A and B and a second signal transmission line including two readout channels C and D, and providing a first signal delay unit and a second signal delay unit on the first signal transmission line and the second signal transmission line; and symbolizing source detectors for forming signals according to pulses of the four readout channels A, B, C and D, and obtaining final pulse information.

A method for scintillation event localization in a radiation particle detector includes providing a plurality of scintillator element locations (2) configured to emit a burst of photons responsive to a radiation particle being absorbed at the scintillator element location (2). A burst of photons emitted by the scintillator element location (2) is detected with a photosensor (5). The photosensor (5) includes an array of single photon avalanche diodes configured to break down responsive to impingement of a photon. Breakdown data (30) is acquired indicative of which of the single photon avalanche diodes are in breakdown. Predetermined photosensor sensitivity data (20, 40) assigns single photon avalanche diodes to groups. Each group is assigned to exactly one scintillator element location (2). Finally the number of single photon avalanche diodes in breakdown is determined for each group individually to identify the scintillator element location (2) that emitted the burst of photons.

The present disclosure relates to a radiation sensor. In one implementation, the sensor may include a radiation detector array having a plurality of pixels; at least two readout connectors having a plurality of contacts, each readout connector being configured for receiving a readout module; a routing circuit having conductors configured for routing electrical signals from each of the plurality of pixels to a corresponding contact of one of the readout connectors. The plurality of pixels is grouped in two or more groups of pixels, at least two pixels of a first group of pixels being separated by at least one pixel from another group of pixels. The routing circuit is configured for leading pixels of the first group of pixels to a first readout connector, and pixels from the other group of pixels to a second readout connector.

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.