A nuclear scanner includes an annular support structure (12) which supports a plurality of radiation detector units (14), each detector unit including crystals (52), tiles (66) containing an array of crystals, or modules (14) of tiles. The detector units define annular ranks of crystals, and the annular ranks of crystals define spaces between the ranks. In another embodiment, the crystals define axial spaces between crystals. Separate rings of crystals have axial spaces that are staggered such that no area of the imaging region is missed. The spaces between the detector units may be adjusted to form uniform or non-uniform spacing. Moving the patient through the annular support structure compensates for reduced sampling under the spaces between ranks.

The present invention relates to a multimodal system for obtaining senological images by means of X-ray and MBI techniques.

Said multimodal system comprises: a supporting plane (1) for the breast, a gamma ray detector (2A) for obtaining at least a molecular image, a detection module (10) comprising inside said gamma ray detector (2A), where said gamma ray detector (2A) is arranged on a first plane, parallel to said supporting plane, as well as: at least one between an X-ray detector (4) for obtaining at least an X-ray image and a scintigraphic collimator (2B); said scintigraphic collimator (2B), when in use, being coupled with said gamma ray detector (2A) and forming with said gamma ray detector (2A) a first gamma camera (2); a compartment (3) configured for receiving one at time said X-ray detector (4) or said scintigraphic collimator (2B), where said compartment (3) is arranged between said supporting plane (1) and said gamma ray detector (2A) on a second plane, parallel to said supporting plane (1), different from said first plane.

A storage phosphor panel can include an extruded inorganic storage phosphor layer including a thermoplastic polymer and an inorganic storage phosphor material, where the extruded inorganic storage phosphor panel has an image quality comparable to that of a traditional solvent coated inorganic storage phosphor screen. Further disclosed are certain exemplary method and/or apparatus embodiments that can provide inorganic storage phosphor panels including a selected blue dye that can improve resolution. Certain exemplary storage phosphor panels include inorganic storage phosphor material with specific extrudable blue dye (copper phthalocyanine) for resolution greater than 16 line pairs per mm. Certain exemplary storage phosphor panel embodiments include any non-needle storage phosphor panel with resolution greater than or equal to 19 line pairs per mm.

A storage phosphor panel can include an extruded inorganic storage phosphor layer including a thermoplastic polymer and an inorganic storage phosphor material, where the extruded inorganic storage phosphor panel has an image quality comparable to that of a traditional solvent coated inorganic storage phosphor screen. Further disclosed are certain exemplary method and/or apparatus embodiments that can provide inorganic storage phosphor panels including reduced noise. Further disclosed are certain exemplary method and/or apparatus embodiments that can include inorganic storage phosphor layer including at least one polymer, an inorganic storage phosphor material, and a copper phthalocyanine based blue dye.

The present invention relates generally to X-ray detectors and more particularly to a system and a method for integrating an anti-scattering grid with scintillators to significantly enhance the performance of flat panel X-ray detector. In particular, the performance of a flat panel X-ray detector may be enhanced by photon counting detector pixels configured underneath the septa of a 2D antiscatter grid.

A radiation therapy apparatus capable of improving the accuracy of a dose distribution includes an X-ray generation device that is provided at an arm portion of a rotation gantry, a radiation detector that is insertable into the body of a patient, a dose calculation device, and a feedback control device. An X-ray generated due to collision of an electron beam with a target in the X-ray generation device is applied to an affected part (cancer) of a patient on a bed. The radiation detector which is insertable into the body detects the X-ray applied to the affected part so as to output a photon to obtain a dose rate and a dose based thereon. The feedback control device either controls the X-ray generation device such that the obtained dose becomes a set dose or controls the radiation generation device such that the obtained dose rate becomes a set dose rate.

A continuous dynamic positron emission tomography (PET) assembly for imaging a target region of a subject. The assembly includes a radioactive tracer isotope injector configured to administer a radioactive isotope into the subject and a scintillator crystal configured to absorb ionizing radiation from the subject and emit scintillator light. The scintillator crystal undertakes the absorption substantially at the same time of the start of administering the radioactive isotope. The assembly also includes a photo detector in communication with the scintillator crystal, wherein the photodetector is configured to detect the emitted scintillation light as input and provide electrical signals as output. The assembly further includes a signal digitizing circuitry converting the output electrical signals into digital data. Moreover, the assembly includes a processor configured to receive the digital data and implement a model to convert the digital data into a three dimensional, tomographic image reconstruction.

A time-of-flight positron emission tomography (TOFPET) assembly for detecting lesions of a breast of a subject, wherein the subject may anatomically be defined with a median plane and chest wall-coronal plane. The assembly may comprise: a detector array having at least two or more detector segments. The detector segments may include: a scintillator for placement toward the target, the scintillator having a top edge generally closest to the subject and a detection surface wall aligned closest to surrounding the breast, a photo multiplier opposite the scintillator, and a readout connected to the photo multiplier. The assembly may also comprise a processor that receives the acquired tracer emission signals and converts the signals into a three dimensional, tomographic image reconstruction. The detector array is defined by a ring surrounding the breast and the face of ring that may be tilted to offset the chest wall-coronal plane of the subject, and wherein one of the top edges of one of the detector segments is above the chest wall-coronal plane of the subject in the posterior direction.

A radiation image capturing apparatus includes a pixel array including conversion elements arranged in rows and columns on an optically transparent substrate, signal lines that outputs a signal generated by the conversion elements and that extends in a column direction, a first scintillator disposed near a first surface of the substrate, and a second scintillator disposed near a second surface of the substrate opposite the first surface. The conversion elements include first conversion elements and second conversion elements. A light shielding layer is disposed between the first scintillator and the second conversion elements such that an amount of light that is received by the second conversion elements from the first scintillator is smaller than that received by the first conversion elements. A number of columns of the conversion elements is equal to a number of the signal lines.

A control unit corrects a lag component, which is included in offset image data in a state in which radiation is not emitted for a period from the end of a first imaging operation of generating second radiographic image data in a state in which the radiation is emitted and to the start of a second imaging operation of generating the second radiographic image data in the state in which the radiation is emitted and at each of a plurality of different times elapsed since the first imaging operation, on the basis of a combination of the correction image data and the time elapsed since the first imaging operation, lag component time change information, and a time from the end of the first imaging operation to the start of the second imaging operation, and corrects the second radiographic image data using the corrected offset image data.