The present disclosure relates to a PET detector and a PET frame. The PET detector may include a plurality of detector modules and a plurality of installing modules configured to install the plurality of detector modules. The plurality of installing modules may be coupled together to form a detector ring. The PET frame may include a detector stabilizing cylinder configured to stabilize a detector and a fixing support configured to support the detector stabilizing cylinder. The detector stabilizing cylinder may be rotatably fixed on the fixing support.

The present invention relates to a radiation detector (100) comprising: i) a substrate (110); ii) a sensor, which is coupled to the substrate, the sensor comprising a first array (120) of sensor pixels, a second array (130) of signal read-out elements, and an electronic circuitry which is configured to provide image data based on signals received from the signal read-out elements; iii) a transducer, which is coupled to the substrate and to the sensor, the transducer comprising a third array (140) of subpixels, wherein at least two subpixels are assigned to one sensor pixel; wherein the second array of signal read-out elements and the third array of subpixels correspond to each other; wherein each of the subpixels comprises a radiation conversion material.

A medical imaging tool is described, capable of providing in real time 2-D images of the prompt gamma fields released during patient treatment. Owing to its millimetre position accuracy, the instrument is particularly suited for applications where a precise determination of the end-of-range (Bragg peak) of the beam is of paramount importance, as in cancerous and non-cancerous targets for treatment with ion beams and for the treatment of atrial fibrillation. With its unique dual-layer conception in coincidence, the instrument has high rejection ability against false neutron-generated counts, the principal source of background noise for in-beam dose monitoring. It can also provide a coarse measurement of the gamma incidence angle, permitting a correction of the parallax error, main source of dispersion for large area detectors employing collimators.

A medical imaging tool is described, capable of providing in real time 2-D images of the prompt gamma fields released during patient treatment. Owing to its millimetre position accuracy, the instrument is particularly suited for applications where a precise determination of the end-of-range (Bragg peak) of the beam is of paramount importance, as in cancerous and non-cancerous targets for treatment with ion beams and for the treatment of atrial fibrillation. With its unique dual-layer conception in coincidence, the instrument has high rejection ability against false neutron-generated counts, the principal source of background noise for in-beam dose monitoring. It can also provide a coarse measurement of the gamma incidence angle, permitting a correction of the parallax error, main source of dispersion for large area detectors employing collimators.

Examples of the present disclosure relate to a particle beam dose profile measurement apparatus comprising a particle detector stack comprising a plurality of scintillator layers. Each scintillator layer of the detector stack is disposed along an axis of the apparatus such that the axis projects through each layer. Each scintillator layer is configured to produce scintillation light indicative of an energy deposition, in that scintillator, of a particle beam incident upon the detector stack along said axis. The apparatus comprises readout circuitry configured to measure the scintillation light of each scintillator layer; and dose profile determination circuitry configured to determine a dose profile of said particle beam within the detector stack. Said determining is based on the measured scintillation light of each scintillator layer, and a quenching correction.

A detector module is provided. The detector module may include a plurality of detector sub-modules. Each of the plurality of detector sub-modules may include a detection layer, at least one data acquisition circuitry, a frame for supporting the detection layer, and a positioning element for assembling the plurality of detector sub-modules. The frame may include a plurality of heat transfer fins that are thermally connected with the at least one data acquisition circuitry for dissipating heat produced by the at least one data acquisition circuitry.

An ion detector according to this embodiment has a structure for reducing influences of signal reflection or the like on an output signal. The ion detector comprises an electron multiplier, a signal output unit, a signal output terminal, and an AC coupler. The AC coupler is disposed on a signal line between the signal output unit and the signal output terminal, including a resin sheet and a pair of conductive sections facing each other with the resin sheet interposed therebetween. One conductive section is electrically connected to an output terminal of the signal output unit, and the other conductive section is electrically connected to the signal output terminal.

An ion detector according to this embodiment has a structure for reducing influences of signal reflection or the like on an output signal. The ion detector comprises an electron multiplier, a signal output unit, a signal output terminal, and an AC coupler. The AC coupler is disposed on a signal line between the signal output unit and the signal output terminal, including a resin sheet and a pair of conductive sections facing each other with the resin sheet interposed therebetween. One conductive section is electrically connected to an output terminal of the signal output unit, and the other conductive section is electrically connected to the signal output terminal.

A positron emission tomography apparatus according to an embodiment includes a plurality of positron emission tomography (PET) detector entities and processing circuitry. The plurality of PET detector entities are arranged in a ring formation. The processing circuitry is configured: to obtain, with respect to each of the plurality of PET detector entities, state information indicating a state of the PET detector entity; to detect an abnormality when an index value indicating a state of any individual or a whole of the plurality of PET detector entities exceeds a threshold value on the basis of the state information; and to detect a state in which the abnormality is not detected on the basis of the state information, but an index value indicating states of at least two of the plurality of PET detector entities is different from an index value indicating states of at least two other PET detector entities.

A particle detector according to one embodiment includes: superconductive lines, conductive lines, insulating films, a first detection circuit, and a second detection circuit. The superconductive lines extend in a first direction and are arranged in a second direction intersecting the first direction. The conductive lines extend in a third direction different from the first direction and are arranged in a fourth direction intersecting the third direction. The insulating films are each interposed at an intersection point between one of the superconductive lines and one of the conductive lines. The first detection circuit detects a voltage change occurring in the superconductive lines. The second detection circuit detects a current or a voltage generated in the conductive lines when the voltage change occurs.