An electromagnetic wave detector is provided. The electromagnetic wave detector comprises: a base; a sensor element arranged on a principal surface of the base and configured to convert, into an electrical signal, light emitted from a scintillator which receives an electromagnetic wave; a lens portion arranged between the scintillator and the sensor element and configured to collect the light generated by the scintillator to the sensor element; a light transmissive portion arranged between the lens portion and the sensor element and configured to transmit the light generated by the scintillator; and a shielding portion including an inner wall located on a periphery of the sensor element and configured to shield the electromagnetic wave. The inner wall is arranged between the light transmissive portion and the principal surface.

A PET detecting module may include a scintillator array configured to receive a radiation ray and generate optical signals in response to the received radiation ray. The scintillator array may have a plurality of rows of scintillators arranged in a first direction and a plurality of columns of scintillators arranged in a second direction. A first group of light guides may be arranged on a top surface of the scintillator array along the first direction. The light guide count of the first group of light guides may be less than the row count of the plurality of rows of scintillators. A second group of light guides may be arranged on a bottom surface of the scintillator array. The light guide count of the second group of light guides may be less than the column count of the plurality of columns of scintillators.

A radiation detector can include a scintillator having opposing end surfaces and a plurality of discrete photosensors disposed on an end surface of the scintillator. In an embodiment, the photosensors are disposed at the corners or along the peripheral edge of the end surface, as opposed to being disposed at the center of the end surface. In an embodiment, the plurality of discrete photosensors may cover at most 80% of a surface area of the end surface of the scintillator and may not cover a center of the end surface of the scintillator. In a further embodiment, an aspect ratio of the monolithic scintillator can be selected to improve energy resolution.

The invention provides a novel arrangement of photon sensors on a scintillation-crystal based gamma-ray detector that takes advantage of total internal reflection of scintillation light within the scintillation detector substrate. The present invention provides improved spatial resolution including depth-of-interaction (DOI) resolution while preserving energy resolution and detection efficiency, which is especially useful in small-animal or human positron emission tomography (PET) or other techniques that depend on high-energy gamma-ray detection. Moreover, the new geometry helps reduce the total number of readout channels required and eliminates the need to do complicated and repetitive cutting and polishing operations to form pixelated crystal arrays as is the standard in current PET detector modules.

A PET detecting module may include a scintillator array configured to receive a radiation ray and generate optical signals in response to the received radiation ray. The scintillator array may have a plurality of rows of scintillators arranged in a first direction and a plurality of columns of scintillators arranged in a second direction. A first group of light guides may be arranged on a top surface of the scintillator array along the first direction. The light guide count of the first group of light guides may be less than the row count of the plurality of rows of scintillators. A second group of light guides may be arranged on a bottom surface of the scintillator array. The light guide count of the second group of light guides may be less than the column count of the plurality of columns of scintillators.

An imaging device includes: a scintillator layer; and an array of photodiode elements; wherein the scintillator layer is configured to receive radiation that has passed through the array of photodiode elements. An imaging device includes: a scintillator layer having a plurality of scintillator elements configured to convert radiation into photons; and an array of photodiode elements configured to receive photons from the scintillator layer, and generate electrical signals in response to the received photons; wherein at least two of the scintillator elements are separated by an air gap. An imaging device includes: a first scintillator layer having a plurality of scintillator elements arranged in a first plane; and a second scintillator layer having a plurality of scintillator elements arranged in a second plane; wherein the first scintillator layer and the second scintillator layer are arranged next to each other and form a non-zero angle relative to each other.

A multi-functional and multi-modality radiation detector (10) is provided. The radiation detector (10) comprises at least two detector units (12a, 12b) having photosensitive pixels (14) and at least one scintillation device (20) optically coupled to the photosensitive pixels (14). The detector units (12a, 12b) are arranged next to each other on a substrate foil (24). Therein, the scintillation devices (20) of the detector units (12a, 12b) are spaced apart from each other, such that the radiation detector (10) is bendable. This allows the radiation detector (10) to be used in many different geometrical configurations.

Dual layer detector (XD) for X-ray imaging, comprising at least two light sensitive surfaces (LSS1,LSS2). The dual layer detector further comprises a first scintillator layer (SL, SL1) including at least one scintillator element (SE) capable of converting X-radiation into light, the element having two faces, an ingress face (S1) for admitting X-radiation into the element (SE) and an egress face (S2) distal from the ingress face (S1), wherein the two faces (S1,S2) are arranged shifted relative to each other, so that a longitudinal axis (LAX) of the scintillator element (SE) is inclined relative to a normal (n) of the layer. The scintillator element (SE) has a sidewall (w,w1) extending between the two faces (S1,S2), the scintillator layer (SL) further comprising a second such scintillator element (SE′) having a sidewall (w′,w1′), the second scintillator element (SE′) neighboring the first scintillator element (SE), wherein the sidewall (w,w1) of the first scintillator element (SE) and the sidewall (w′,w1′) of the second scintillator element (SE′) are neighbored and are inclined relative to each other. The dual layer detector (XD) further comprises a second such scintillator layer (SL2). One of the light sensitive surfaces (LSS1,LSS2) is arranged in between the two scintillator layers (SL1, SL2).

A method and apparatus for testing the response of protective headgear 104 to impact forces. A high-speed cineradiography imaging system 100 is used to obtain full-field, time-resolved internal monitoring and measurement of headgear component (pads 140 and liners 142) deformation and interaction with a head surrogate (headform 102), deformation of headform components, and stress and strain transfer into the headform. Radiopaque contrast materials (144 & 148) and integration techniques are used to highlight specific regions of interest within the headgear and headform components during the impact loading events.

A gamma-ray detector includes a plurality of modular one-dimensional arrays of monolithic detector sub-modules. Each monolithic detector sub-module includes a scintillator layer, a light-spreading layer, and a photodetector layer. The photodetector layer comprises a two-dimensional array of photodetectors that are arranged in columns and rows. A common printed circuit board is electrically coupled to the photodetectors of the monolithic detector sub-modules of a corresponding modular one-dimensional array. The photodetectors can be electrically coupled in a split-row configuration or in a checkerboard configuration. The photodetectors can also have a differential readout.