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:
An imaging system (10) includes a first imaging device (12); a second imaging device (14) of a different modality than the first imaging device; a display device (24); and at least one electronic processor (20) programmed to: operate the first imaging device to acquire first imaging data of a subject; operate the second imaging device to acquire second imaging data of the subject; compare the first imaging data and the second imaging data to detect a possible fault in the second imaging device; and control the display device to present an alert indicating the possible fault in the second imaging device in response to the detection of the possible fault in the second imaging device.
Abstract:
The present invention relates to a detector (10) for a dark-field and/or phase-contrast interferometric imaging system. The detector comprises a plurality of pixels (50), a plurality of first detector arrays (20), a plurality of second detector arrays (30), and a processing unit (40). The plurality of pixels are arranged in a two-dimensional pattern. Each pixel comprises a first detector array and a second detector array. Each first detector array comprises a plurality of fingers (22). Each second detector array comprises a plurality of fingers (32). For each pixel the fingers of the first detector array are interleaved alternately with the fingers of the second detector array. For each pixel interaction with an incident X-ray photon can lead to charge generation in at least one finger of the first detector array of that pixel and can lead to charge generation in at least one finger of the second detector array of that pixel. For each pixel the first detector array is configured to detect a cumulative charge associated with the plurality of fingers of the first detector array and the second detector array is configured to detect a cumulative charge associated with the plurality of fingers of the second detector array. For each pixel the processing unit is configured to assign an X-ray interaction event to either the first detector array or the second detector array on the basis of the detector array that has the highest cumulative charge.
Abstract:
The invention relates to a scintillator array for a radiation imaging detector. A method for manufacturing the scintillator array, a radiation imaging detector, and a medical imaging system are also provided. The scintillator array has a radiation receiving face and an opposing scintillation light output face. The scintillator array includes a plurality of scintillator elements and a separator material that is disposed between the scintillator elements. The separator material consists of separator particles that have a predetermined size and with this the separator material provides an optical separation of the scintillator elements by providing a physical spacing between the scintillator elements, the width of which spacing is defined by the separator particle size.
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 front photosensor layer (2) configured to detect scintillation photons generated in the front scintillator layer (3), wherein the high-energy radiation quantum is a gamma ray and the low-energy radiation quantum is an X-ray.
Abstract:
The present invention relates to a combined imaging detector (10, 20) for detection of gamma and x-ray quanta comprising an integrating x-ray detector (11) comprising a first scintillator layer (12) and a photodetector array (13) and a second structured scintillator layer (14), optionally as part of a second gamma detector having a second photodetector array. The combined imaging detector can be used for X-ray and SPECT detection and uses the principle of current flat x-ray detectors. Different resolutions are used: high spatial resolution for x-ray imaging and low spatial resolution for SPECT imaging.
Abstract:
The invention relates to an analyzing grid for phase contrast imaging and/or dark-field imaging, a detector arrangement for phase contrast imaging and/or dark-field imaging comprising such analyzing grid, an X-ray imaging system comprising such detector arrangement, a method for manufacturing such analyzing grid, a computer program element for controlling such analyzing grid or detector arrangement for performing such method and a computer readable medium having stored such computer program element. The analyzing grid comprises a number of X-ray converting gratings. The X-ray converting gratings are configured to convert incident X-ray radiation into light or charge. The number of X-ray converting gratings comprises at least a first X-ray converting grating and a second X-ray converting grating. Further, the X-ray converting gratings each comprise an array of grating bars, wherein the grating bars within each X-ray converting grating are arranged mutually displaced from each other in a direction perpendicular to the incident X-ray radiation by a specific displacement pitch. Further, the grating bars of the first X-ray converting grating are arranged mutually displaced from the grating bars of the second X-ray converting grating in the direction perpendicular to the incident X-ray radiation by the displacement pitch divided by the number of X-ray converting gratings.
Abstract:
The invention relates to a system for imaging an object in an x-ray imaging mode and in a gamma imaging mode. A radiation detector (1) of the system comprises a conversion unit (202) including a plurality of detector pixels (206 1,...,M ) and generating for each detection event a detection signal indicative of an energy of the event, and a counting unit (203) including for each detector pixel (206 1,...,M ) a plurality of comparators (209 i;1,...,N ) and associating each detection event to one of a plurality of predetermined energy bins based on the detection signals using the comparators (209 i;1,...,N ). In the x-ray imaging mode, the comparators(209 i;1,...,N ) of one pixel (206 1,...,M ), and, in the gamma imaging mode, the comparators (209 i;1,...,N ) of several pixels (206 1,...,M ) are available for the association so that more energy bins are available in the gamma imaging mode than in the x-ray imaging mode.
Abstract:
The invention relates to a gamma radiation detector that provides compensation for the parallax effect. The gamma radiation detector (100) includes a plurality of scintillator elements (101), a planar optical detector array (102), and a pinhole collimator (103) that includes a pinhole aperture (104). Each scintillator element has a gamma radiation receiving face (101') and an opposing scintillation light output face (101''). The gamma radiation receiving face of each scintillator element faces the pinhole aperture for generating scintillation light in response to gamma radiation received from the pinhole aperture. The scintillator elements are arranged in groups (105). Each group has a group axis (106) that is aligned with the pinhole aperture (104) and is perpendicular to the radiation receiving face of each scintillator in that group. The scintillation light output faces of each of the scintillator elements are in optical communication with the planar optical detector array (102).