Abstract: The invention relates to a ceramic material (14) for generating light when irradiated with radiation, wherein the ceramic material comprises a stack of layers (15, 16) having different compositions and/or different dopings. The ceramic material may be used in a spectral computed tomography (CT) detector, in order to spectrally detect x-rays, or it may be used as a ceramic gain medium of a laser such that temperature gradients and corresponding thermo-mechanical stresses within the gain medium can be reduced.

Abstract: The invention relates to a combined imaging detector (110) for the detection of x-ray and gamma quanta. The combined imaging detector (110) is adapted for simultaneous detection of gamma and x-ray quanta. The combined imaging detector (110) includes an x-ray anti-scatter grid (111), a layer of x-ray scintillator elements (112), a first photodetector array (113), a layer of gamma scintillator elements (114), and a second photodetector array (115) that are arranged in a stacked configuration along a radiation-receiving direction (116). The x-ray anti-scatter grid (111) comprises a plurality of septa (117A, B, C) that define a plurality of apertures (118) which are configured to collimate both x-ray quanta and gamma quanta received from the radiation receiving direction (116) such that received gamma quanta are collimated only by the x-ray anti-scatter grid (111). The use of the x-ray anti-scatter grid as a collimator for received gamma quanta results in a significantly lighter combined imaging detector.

Abstract: A whole body SPECT system (10) includes a patient support (14) and a static gantry (12) which includes a plurality of rings (40a,40b,40c) of radiation detectors (42). The patient support (14) supports a patient and moves the patient in an axial direction (18) through the static gantry (12). One or more processors (20,24,32) connected to the plurality of detectors records strikes of gamma photons in the radiation detectors (42) and reconstruct the recorded strikes of the gamma photons into a whole body image.

Abstract: The invention relates to the detection of x-ray and gamma quanta. In the medical imaging arrangement (100) an x-ray source (111) is attached to a first portion of an x-ray c-arm (113) and an x-ray detector (112) is attached to a second portion of the x-ray c-arm (113) for measuring x-ray transmission along a path (115) between the x-ray source and the x-ray detector. A gamma camera (114) is movable along a trajectory (116) that intersects the path between the x-ray source and the x-ray detector. Since the gamma camera can be moved along a trajectory that intersects the path between the x-ray source and the x-ray detector, the gamma camera can be used to generate a nuclear image that closely corresponds to the same region of interest as that which is imaged by the x-ray source and detector.

Abstract: An improved scintillator nanocomposite comprising nanoparticles with scintillating properties and a diameter between 10 and 50 nanometer and a first matrix material comprises is obtained by introducing the nanoparticles into a dispersing medium to form a stable suspension. The dispersing medium is a precursor to the first matrix material, which is cured to form the first matrix material.

Abstract: The invention relates to a characterization apparatus (1) for characterizing scintillator material (3) especially for a PET detector. A first radiation source (2) irradiates the scintillator material with first radiation (4) having a wavelength being smaller than 450 nm. Then, a second radiation source (5) irradiates the scintillator material with pulsed second radiation (6) having a wavelength being larger than 600 nm and having a pulse duration being equal to or smaller than 50 s, wherein a detection device (9) detects third radiation (12) from the scintillator material (3) during and/or after the irradiation by the second radiation. The third radiation depends on the amount of charge carriers trapped at electronic defects of the scintillator material such that it can be used as an indicator for the amount of electronic defects and hence for characterizing the scintillator material. This characterization can be performed relatively fast and in a relatively simple way.

Abstract: A radiation detector for combined detection of low-energy radiation quanta and high-energy radiation quanta, the radiation detector (8) having a multi-layered structure, comprising: a rear scintillator layer (5) configured to emit a burst of scintillation photons responsive to a high-energy radiation quantum being absorbed by the rear scintillator layer (5); a rear photosensor layer (6) attached to a back side of the rear scintillator layer (5), said rear photosensor layer (6) configured to detect scintillation photons generated in the rear scintillator layer (5); a front scintillator layer (3) arranged in front of the rear scintillator layer (5) opposite the rear photosensor layer (6), said front scintillator layer (3) configured to emit a burst of scintillation photons responsive to a low-energy radiation quantumbeing absorbed by the front scintillator layer (3); and a front photosensor layer (2) attached to a front side of the front scintillator layer (3) opposite the rear scintillator layer (5), said fron

Abstract: The invention relates to a method for producing a radiation detector used to detect ionizing radiation including a first inorganic-organic halide Perovskite material (24) as a direct converter material and/or as a scintillator material in a detector layer and to a radiation detector comprising a detector layer (24) produced by means of the steps of the method. In order to provide an approach for producing a thick layer (e.g. above 10 ???) of Perovskite material suitable for a radiation detector, it is proposed to grow the material selectively on a seeding layer (23), yielding in a thick polycrystalline layer. One suitable seeding layer (23) to grow lead Perovskite material is made of a bromide Perovskite material.

Abstract: The present invention relates to a direct conversion radiation detector for wherein the direct conversion material comprises a garnet with a composition of Z3(AlxGay)O12:Ce, wherein Z is Lu, Gd, Y, Tb or combinations thereof and wherein y is equal to or greater than x; and preferably Z comprises Gd. Suitable garnets directly convert radiation, such as x-rays or gamma-rays, into electronic signals. Preferably photoluminescence of the garnet is low or absent. The detector is particularly suitable for use in x-ray imaging devices, such as computed tomography. In some embodiments photoluminescence of garnets might be used to construct a hybrid direct-indirect conversion detector, which may be particularly suitable for use with Time-of-Flight PET.

Abstract: The present invention relates to a direct conversion radiation detector for wherein the direct conversion material comprises a garnet with a composition of Z3(AlxGay)O12:Ce, wherein Z is Lu, Gd, Y, Tb or combinations thereof and wherein y is equal to or greater than x; and preferably Z comprises Gd. Suitable garnets directly convert radiation, such as x-rays or gamma-rays, into electronic signals. Preferably photoluminescence of the garnet is low or absent. The detector is particularly suitable for use in x-ray imaging devices, such as computed tomography. In some embodiments photoluminescence of garnets might be used to construct a hybrid direct-indirect conversion detector, which may be particularly suitable for use with Time-of-Flight PET.

Abstract: A multimodal imaging apparatus (1a, 1b) including scintillator elements (31) for capturing incident gamma quanta (25, 61) and for emitting scintillation photons (26) in response to said captured gamma quanta (25, 61). Photosensitive elements (33) capture the emitted scintillation photons (26) and determine a spatial distribution of the scintillation photons. The imaging apparatus (1a, 1b) is configured to be switched between a first operation mode for detecting low energy gamma quanta and a second operation mode for detecting high energy gamma quanta. The scintillator elements are arranged to capture incident gamma quanta (25, 61) from the same area of interest (65) in both operation modes. The scintillator elements (31) include a first region with high energy scintillator elements (27) for capturing high energy gamma quanta and a second region with low energy scintillator elements (29) for capturing low energy gamma quanta.

Abstract: A ceramic or polycrystalline scintillator composition is represented by the formula (LuyGd3-y)(GaxAl5-x)O12:Ce; wherein y=1±0.5; wherein x=3±0.25; and wherein Ce is in the range 0.01 mol % to 0.7 mol %. The scintillator composition finds application in the sensitive detection of ionizing radiation and may for example be used in the detection of gamma photons in the field of PET imaging.

Abstract: A radiation detection device detects gamma or x-ray radiation quanta with improved timing accuracy and improved energy resolution. The radiation detection device finds application in the detection of gamma and x-ray radiation and may be used in the field of PET imaging, and in spectral CT. The radiation detection device includes a semiconductor scintillator element and a photodetector. The photodetector is in optical communication with the scintillator element. The scintillator element has two mutually opposing faces; a cathode is in electrical communication with one of the two faces and an anode is in electrical communication with the other of the two faces.

Abstract: The invention relates to a detector (6) for detecting radiation, especially x-ray radiation used in a computed tomography system. The detector comprises a direct conversion material (9) for converting radiation into electrons and holes, which are used for generating an electrical detection signal. The direct conversion material is illuminated with illumination light being broadband visible and/or broadband infrared light for reducing, in particular, eliminating, a polarization of the direct conversion material, which may occur when being traversed by the radiation to be detected and which may reduce the detection performance. By reducing the polarization of the direct conversion material the detection performance can be improved.

Abstract: The invention relates to a characterization apparatus (1) for characterizing scintillator material (3) especially for a PET detector. A first radiation source (2) irradiates the scintillator material with first radiation (4) having a wavelength being smaller than 450 nm. Then, a second radiation source (5) irradiates the scintillator material with pulsed second radiation (6) having a wavelength being larger than 600 nm and having a pulse duration being equal to or smaller than 50 s, wherein a detection device (9) detects third radiation (12) from the scintillator material (3) during and/or after the irradiation by the second radiation. The third radiation depends on the amount of charge carriers trapped at electronic defects of the scintillator material such that it can be used as an indicator for the amount of electronic defects and hence for characterizing the scintillator material. This characterization can be performed relatively fast and in a relatively simple way.

Abstract: A gamma photon detector for detecting 511 keV PET radiation includes a scintillator host material doped with cerium. The cerium is present in a concentration of 0.1 to 1.0 mol %. Lower concentrations increase light output but also decay times which can lead to pile up issues. The higher light output enables the read out area to be decreased which reduces the pile up issues. Embodiments with a cerium concentration as low as 0.15 to 0.2 mol % and a read out area as low as 0.1 cm2 are contemplated.

Abstract: A gamma radiation detection device (1) includes a scintillator element (2) and an optical detector (3) in optical communication with the scintillator element (2). A plurality of particles or voids (5) are dispersed in the scintillator element (2) which scatter the scintillation light (7), reducing the trapping of scintillation light (7) by multiple reflections.

Abstract: The present invention relates to a ceramic or polycrystalline scintillator composition represented by the formula (LUy-Gd3-y)(GxAI5-x)O12: Ce; wherein y=1±0.5; wherein x=3±0.25; and wherein Ce is in the range 0.01 mol % to 0.7 mol %. The scintillator composition finds application in the sensitive detection of ionizing radiation and may for example be used in the detection of gamma photons in the field of PET imaging.

Abstract: The present invention relates to a multimodal imaging apparatus (1a, 1b) for imaging a process (63) in a subject (23), said process (63) causing the emission of gamma quanta (25, 61), said apparatus (1a, 1b) comprising a scintillator (3) including scintillator elements (31) for capturing incident gamma quanta (25, 61) generated by the radiotracer and for emitting scintillation photons (26) in response to said captured gamma quanta (25, 61), a photodetector (5) including photosensitive elements (33) for capturing the emitted scintillation photons (26) and for determining a spatial distribution of the scintillation photons, and a readout electronics (7) for determining the impact position of an incident gamma quantum in the scintillator (3) and/or a parameter indicative of the emission point of the gamma quantum (25, 61) in the subject (23) based on the spatial distribution of the scintillation photons, wherein the imaging apparatus (1a, 1b) is configured to be switched between a first operation mode for detect

Abstract: The present invention relates to a radiation detection device for detecting gamma or x-ray radiation quanta with improved timing accuracy and improved energy resolution. The radiation detection device finds application in the detection of gamma and x-ray radiation and may be used in the field of PET imaging, and in spectral CT. The radiation detection device includes a semiconductor scintillator element and a photodetector. The photodetector is in optical communication with the scintillator element. The scintillator element has two mutually opposing faces; a cathode is in electrical communication with one of the two faces and an anode is in electrical communication with the other of the two faces.