The present invention provides a method of calibrating gamma-ray and photon counting detectors, including, but not limited to, monolithic crystal detectors. The method of the present invention is based on the observation that measurement of fan beam datasets allows the synthesis of collimated beam data to derive MDRFs by use of an algorithm that finds the common or intersecting data subsets of two or more orthogonal calibration datasets. This makes the calibration process very efficient while still allowing the full benefits of maximum-likelihood event-parameter estimation that incorporates the statistical nature of the light sensor measurements.

A nuclear radiation monitoring apparatus comprising: communication circuitry configured to receive nuclear radiation data generated by a nuclear radiation detector, the nuclear radiation data being indicative of nuclear radiation emitted from each of a plurality of portions of an object and detected by the nuclear radiation detector; classification circuitry configured to classify the detected nuclear radiation using the nuclear radiation data; intensity determination circuitry configured to determine a value of an intensity parameter indicative of an intensity of the classified nuclear radiation for each portion of the object using the nuclear radiation data; visualisation data generation circuitry configured to generate visualisation data indicative of the classification of the classified nuclear radiation and, for each portion of the object, visualisation data indicative of the portion of the object and the determined intensity parameter value of the portion of the object; and display output circuitry configured to output the generated visualisation data for display.

A radiation image capturing apparatus includes a sensor substrate including a flexible base material and plural pixels that accumulate charges generated in accordance with radiation, a flexible first cable including one ends electrically connected to a connection region disposed at a predetermined side of the sensor substrate, a first circuit substrate electrically connected to the other end of the first cable and in which a first component used for processing a digital signal in a circuit unit driven in a case of reading out the charges in the plural pixels is mounted, a flexible second cable including one end electrically connected to a connection region disposed at a side different from the predetermined side, and a second circuit substrate electrically connected to the other end of the second cable and in which a second component used for processing an analog signal in the circuit unit is mounted.

An optical measurement device includes: an optical sensor that detects pulsed signal light and that outputs a detection signal formed of an exponential-function response; an A/D converter that samples the detection signal output from the optical sensor and that converts the detection signal into a digital signal; and a processor comprising hardware, the processor being configured to subject the digital signal output from the A/D converter to inverse transformation by using a multiple diagonal matrix, thus calculating an estimated pulse of the signal light.

A time of flight positron emission tomography (TOF PET) detector comprises a direct conversion semiconductor crystal (e.g. CZT), cathode and anode disposed on respective first and opposite second faces of the crystal, and a timing circuit operatively connected to generate a trigger signal in response to absorption of a 511 keV gamma ray by the direct conversion semiconductor crystal. The timing circuit generates the trigger signal with jitter of 500 picoseconds or lower. One or both of the cathode and/or anode is a blocking electrode. In some embodiments, the cathode is a single continuous electrode, the timing circuit is operatively connected with the cathode, the anode comprises an array of electrode pixels disposed on the second face of the direct conversion semiconductor crystal, and a sense circuit is operatively connected with the electrode pixels of the anode. TOF PET scanners including such detectors are also disclosed.

An imaging unit includes a housing having a wall portion in which a slit for passing radiation is formed, a scintillator having an input surface to which radiation passing through the slit is input, a first mirror that reflects scintillation light output from the input surface, and a line scan camera that detects scintillation light reflected by the first mirror. The scintillator is placed to make the input surface parallel to both the conveying direction and a line direction. The first mirror is positioned outside an irradiation region connecting the peripheral edge of the slit to the input surface of the scintillator.

An imaging unit includes a housing having a wall portion in which a slit for passing radiation is formed, a scintillator having an input surface to which radiation passing through the slit is input, a first mirror that reflects scintillation light output from the input surface, and a line scan camera that detects scintillation light reflected by the first mirror. The scintillator is placed to make the input surface parallel to both the conveying direction and a line direction. The first mirror is positioned outside an irradiation region connecting the peripheral edge of the slit to the input surface of the scintillator.

The present invention provides a method of calibrating gamma-ray and photon counting detectors, including, but not limited to, monolithic crystal detectors. The method of the present invention is based on the observation that measurement of fan beam datasets allows the synthesis of collimated beam data to derive MDRFs by use of an algorithm that finds the common or intersecting data subsets of two or more orthogonal calibration datasets. This makes the calibration process very efficient while still allowing the full benefits of maximum-likelihood event-parameter estimation that incorporates the statistical nature of the light sensor measurements.

To optimize an image quality and/or a sensitivity, a Compton camera is adaptable. A scatter detector and/or a catcher detector may move closer to and/or further away from a patient and/or each other. This adaptation allows a balancing of the image quality and the sensitivity by altering the geometry.

To optimize image quality and/or sensitivity, a Compton camera is adaptable. The scatter and/or catcher detectors may move closer to and/or further away from a patient and/or each other. This adaptation allows a balancing of image quality and sensitivity by altering the geometry.