An auxiliary device attachable to a mammography machine having an X-ray source and an X-ray receptor having a receptor area. The auxiliary device includes a housing having a length, width, and thickness, wherein the length and width of the housing are adapted to a length and width of the receptor area. The auxiliary device further includes one or more attachments for attaching the auxiliary device to the mammography machine, and a detector inside the housing. The detector includes a slab of semiconductor material, an electrode on a first side of the slab, and a pixelated electrode detector on the second side of the slab, and a read-out circuit bonded to the pixelated electrode detector, and the read-out circuit being configured for spectral photon counting with two or more energy bins. Methods for medical imaging are also provided.

The invention relates to a combined detector (660) comprising a gamma radiation detector (100) and an X-ray radiation detector (661). The gamma radiation detector (100) comprises a gamma scintillator array (101.sub.x, y), an optical modulator (102) and a first photodetector array (103.sub.a, b) for detecting the first scintillation light generated by the gamma scintillator array (101.sub.x, y). The optical modulator (102) is disposed between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b) for modulating a transmission of the first scintillation light between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b). The optical modulator (102) comprises at least one optical modulator pixel having a cross sectional area (102′) in a plane that is perpendicular to the gamma radiation receiving direction (104). The cross sectional area of each optical modulator pixel (102′) is greater than or equal to the cross sectional area of each photodetector pixel (103′.sub.a, b).

An auxiliary device attachable to a mammography machine having an X-ray source and an X-ray receptor having a receptor area. The auxiliary device includes a housing having a length, width, and thickness, wherein the length and width of the housing are adapted to a length and width of the receptor area. The auxiliary device further includes one or more attachments for attaching the auxiliary device to the mammography machine, and a detector inside the housing. The detector includes a slab of semiconductor material, an electrode on a first side of the slab, and a pixelated electrode detector on the second side of the slab, and a read-out circuit bonded to the pixelated electrode detector, and the read-out circuit being configured for spectral photon counting with two or more energy bins. Methods for medical imaging are also provided.

A radiation image sensing apparatus is provided. The apparatus comprises an image sensing area where conversion elements are arranged and used in an image sensing operation of acquiring a radiation image, a detection element configured to detect a radiation dose of radiation entering the image sensing area, a readout unit and a controller. The controller corrects a detection signal read out from the detection element by the readout unit during incidence of radiation in a second image sensing operation performed next to a first image sensing operation, based on a correction amount acquired based on a correction signal read out from the detection element by the readout unit after an end of the incidence of the radiation in the first image sensing operation, and detects a dose of incident radiation in the second image sensing operation based on the corrected detection signal.

Methods and systems are provided for a medical imaging system having a detector array. In one example, the detector array may include a plurality of adjustable imaging detectors arranged in subsets thereof, each of the plurality of adjustable imaging detectors including a detector unit, each detector unit having a plurality of rows of detector modules, wherein the plurality of adjustable imaging detectors may be arranged on an annular gantry, where an inner surface of the annular gantry may circumscribe a substantially rectangular aperture therethrough, and wherein each subset of the plurality of adjustable imaging detectors may be respectively disposed on a side of the inner surface and may extend within the substantially rectangular aperture.

A radiation image sensing apparatus is provided. The apparatus comprises an image sensing area where conversion elements are arranged and used in an image sensing operation of acquiring a radiation image, a detection element configured to detect a radiation dose of radiation entering the image sensing area, a readout unit and a controller. The controller corrects a detection signal read out from the detection element by the readout unit during incidence of radiation in a second image sensing operation performed next to a first image sensing operation, based on a correction amount acquired based on a correction signal read out from the detection element by the readout unit after an end of the incidence of the radiation in the first image sensing operation, and detects a dose of incident radiation in the second image sensing operation based on the corrected detection signal.

A method of processing a SPECT image of a region of interest is disclosed. The SPECT image was obtained using at least one gamma detector detecting gamma radiation from the region of interest at multiple detector configurations, and the method includes: obtaining data indicative of the detector configurations and their spatial relationships to the region of interest; determining a resolution level for each of a plurality of directions in each point in the image based on the data obtained; and processing the image based on the resolution levels determined.

Detector systems for enhanced radiographic imaging incorporate one or more Compton and nuclear medicine imaging, PET imaging, and x-ray CT imaging capabilities. The detector designs employ one or more layers of detector modules comprising edge-on or face-on detectors, or a combination of edge-on and face-on detectors, which can employ gas, scintillator, semiconductor, low temperature (such as Ge and superconductor) or structured detectors. The detectors implement tracking capabilities, and operate in non-coincidence or coincidence detection modes.

The invention relates to a combined detector (660) comprising a gamma radiation detector (100) and an X-ray radiation detector (661). The gamma radiation detector (100) comprises a gamma scintillator array (101.sub.x, y), an optical modulator (102) and a first photodetector array (103.sub.a, b) for detecting the first scintillation light generated by the gamma scintillator array (101.sub.x, y). The optical modulator (102) is disposed between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b) for modulating a transmission of the first scintillation light between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b). The optical modulator (102) comprises at least one optical modulator pixel having a cross sectional area (102) in a plane that is perpendicular to the gamma radiation receiving direction (104). The cross sectional area of each optical modulator pixel (102) is greater than or equal to the cross sectional area of each photodetector pixel (103.sub.a, b).

Nuclear medicine (NM) imaging system includes a plurality of detector assemblies that each have a movable arm and a detector head that is coupled to the movable arm. The movable arm is configured to move the detector head toward and away from an object. The NM imaging system also includes at least one processor configured to determine a body contour of the object and determine an acquisition configuration using the body contour. The acquisition configuration includes at least three of the detector heads positioned in a dense group that borders the body contour. The detector heads in the dense group are primary detector heads. The at least one processor is also configured to move at least one of the object or one or more of the primary detector heads so that the primary detector heads are in the dense group near the object.