Provided is a method of fabricating a detector array that includes preparing a plurality of slabs of an optical medium of an imaging device, forming a plurality of optical boundaries within at least one of the slabs of optical medium, where the plurality of optical boundaries defining a 1×N array of non-contiguous, independent light-redirecting regions within the at least one slab, arranging the plurality of slabs into a stack with a reflective layer defined between each adjacent slab and affixing the positions of the plurality of slabs with respect to each other. A detector array formed using the method is also provided.

This invention provides a close-range positron emission tomography (PET) system, where the detector modules are able to be moved or placed very close to the patient compared to conventional PET systems. As a result, the sensitivity and resolution of the PET system is greatly increased.

A sensor chip includes a plurality of microcells to which an xy position is assigned, composed of a photodiode D.sub.n,m, a current divider S.sub.q,nm, with outputs S.sub.q,v,nm, for the y direction and outputs S.sub.q,h,nm for the x direction, the outputs S.sub.q,h,nm being equipped with a quenching apparatus R.sub.q,h,nm for quenching the current, and the outputs S.sub.q,v,nm being equipped with a quenching apparatus R.sub.q,v,nm for quenching the current, which divides the generated photocurrent of the diodes Dn,m into two equally large fractions. The microcells are arranged in a sequence of N columns in the x direction x.sub.n,=x.sub.1, x.sub.2, x.sub.3, . . . x.sub.n with n=1, 2, 3, . . . N and M rows in the y direction y.sub.m,=y.sub.1, y.sub.2, y.sub.3, . . . y.sub.m with m=1, 2, 3, . . . M. Outputs S.sub.q,h,nm of the current dividers S.sub.q,nm for the x direction are connected to the read-out channels Ch.sub.A and Ch.sub.B for the x direction.

A scalable medical imaging detector arrangement is provided having interchangeable sensor tiles with fixed outer dimensions for a fixed or universal mechanical, electrical, and cooling interface. Different sensor tile types with different performance grades and production costs care configured with a common interface for coupling to the medical imaging device, while the rest of the imaging system can remain unchanged.

Provided area device for detecting sub-atomic particles and method of fabrication thereof. The device includes a plurality of scintillators, a detector provided on a first end of the plurality of scintillators and a prismatoid provided on a second end of the plurality of scintillators. The prismatoid redirects light between adjacent scintillators of the plurality of scintillators.

Provide are a detector module, a detector, and a medical device. The detector module includes a plurality of detection sub-modules at least partially arranged in a stepped manner in a first direction. Each of the plurality of detection sub-modules includes a plurality of photoelectric conversion units arranged at intervals in a second direction intersecting with the first direction. One of two adjacent detection sub-modules is located at a higher step as a first detection sub-module, and the other one is located at a lower step and as a second detection sub-module. A first gap is formed between the plurality of photoelectric conversion units of the first detection sub-module. A second gap is formed between the plurality of photoelectric conversion units of the second detection sub-module. A width of the first gap in the second direction is smaller than a width of the second gap in the second direction.

The present disclosure relates to a system for PET imaging. The system may include a detector module and an electronics module. The detector module may include a scintillator array having N rows of scintillators arranged in a first direction and M columns of scintillators arranged in a second direction, a first set of photosensors coupled to the scintillator array and extending in the second direction, and a second set of photosensors coupled to the scintillator array and extending in the first direction. The electronics module may detect a first set of electrical signals generated by the first set of photosensors and a second set of electrical signals generated by the second set of photosensors, and identify a scintillator within the scintillator array that has interacted with an impinging radiation ray relating to an electrical signal of the first set of electrical signals or the second set of electrical signals.

A medical imaging system is provided. Imaging detector columns are installed in a gantry to receive imaging information about a subject. Imaging detector columns can extend and retract radially as well as be rotated orbitally around the gantry. The system can automatically adjust setup configuration and an imaging operation based on subject shape estimation information.

The invention relates to a device for the detection of gamma rays (1) coming from a source (2) without image truncation and without image overlapping, comprising, at least, two detection cells (3) and each of said cells comprising a detection space (7) adapted to receive the gamma rays (1) that penetrate through an opening (5), wherein said detection space (7) comprises one or more detection assemblies (8, 8′), with some of said assemblies (8′) being positioned such that they stand in the way of the gamma rays (1) coming into the overlap volume (11) thereof.

A PET detector and method thereof are provided. The PET detector may include: a crystal array including a plurality of crystal elements arranged in an array and light-splitting structures set on surfaces of the plurality of crystal elements, the light-splitting structures jointly define a light output surface of the crystal array; a semiconductor sensor array, which is set in opposite to the light output surface of the crystal array and is suitable to receive photons from the light output surface, the semiconductor sensor array comprises a plurality of semiconductor sensors arranged in an array.