For a multi-modal emission tomography system, an improved control system increases the likelihood of optimal image quality, satisfaction of physician goals, and/or avoids repetition in scanning and the corresponding increase in dose burden. The control system is divided into two or more arrangements. One arrangement receives goal information and outputs reconstruction settings and generic scan settings to satisfy the goal information. Another arrangement converts the generic scan settings to emission tomography system-specific scan settings, which are used to detect emissions. The separation of the arrangements allows independent operation so that different system-specific conversions may be used for different systems. Another possible arrangement performs a quality check on the detected emissions, allowing feedback for altering the system-specific scan settings to possibly avoid scan repetition and/or allowing feedforward for reconstruction to optimize the reconstruction settings based on the acquired data to be reconstructed.

A detector element circuit for a CT imaging system may include a plurality of sensors for detecting photons passing through an object and a first electronic component configured to determine an energy of photons detected by the plurality of sensors and generate photon count data, which may be a count of detected photons in one or more energy bins. The detector element circuit may further include a second electronic component configured to receive the photon count data from the first electronic component and is clocked at a first clock rate; a local memory storage configured to receive the photon count data from the second electronic component at the first clock rate and to output the photon count data at a second clock rate.

A gamma camera, a system, and a method are described, wherein a large gamma camera can be subdivided into two or more smaller gamma cameras, each independently positioned for SPECT data acquisition. These transformable gamma cameras make more efficient use of the gamma photon detector area. Tiled arrays of semiconductor gamma detectors are especially suited for such transformation.

A gamma camera, a system, and a method are described, wherein a large gamma camera can be subdivided into two or more smaller gamma cameras, each independently positioned for SPECT data acquisition. These transformable gamma cameras make more efficient use of the gamma photon detector area. Tiled arrays of semiconductor gamma detectors are especially suited for such transformation.

A radiation detection apparatus includes a plurality of detection substrates on which photoelectrical conversion elements are arranged, a plate configured to support the plurality of detection substrates, a scintillator, and a plurality of bonding material members configured to bond the plurality of detection substrates and the scintillator. The plurality of bonding material members bond one-side surfaces of the plurality of detection substrates and a one-side surface of the scintillator, and the plurality of bonding material members are separated from each other and arranged so that outer edges of the plurality of bonding material members are not positioned between the plurality of detection substrates.

In order to appropriately reduce time until scanning can be started after preparation in both an operation console and a scan room is completed, an X-ray CT apparatus includes an X-ray tube, an X-ray detector, a rotation disk, an image calculation device, a display device, a system control device, an operation console instruction device that instructs the system control device to prepare, start, and stop scanning in an operation console, and a scan gantry instruction device that instructs the system control device to prepare, start, and stop scanning in a scan room, in which the system control device includes a scanning preparation control unit that performs some scanning preparation processes among a plurality of scanning preparation processes on the basis of an instruction for scanning preparation from the operation console instruction device or the scan gantry instruction device.

The present disclosure relates to systems and methods for image data processing. A first correction coefficient corresponding to a first collimation width of a collimator of a scanner may be obtained. The collimator may have a collimation width being adjustable. A relationship between scattered radiation intensities and collimation widths may be obtained. A relationship between correction coefficients and collimation widths may be determined based on the first correction coefficient, the first collimation width, and the relationship between scattered radiation intensities and collimation widths. A target collimation width of the collimator may be obtained. A target correction coefficient may be determined based on the target collimation width and the relationship between correction coefficients and collimation widths.

A radiotherapy system is configured to determine in vivo dose deposition of a radiotherapy treatment beam. The system includes the following components. A bi-planar magnetic resonance imaging (MRI) apparatus comprising a pair of spaced apart magnets. One of the magnets includes a hole proximal the centre thereof. A treatment beam source configured to generate a radiotherapy reatment beam. The treatment beam source is positioned to transmit the treatment beam through the hole in the magnet. A patient support configured to position a patient with the system so that a treatment target is proximal the treatment beam. A Positron Emission Tomography (PET) detector configured to obtain PET data of the treatment beam impacting the patient. The PET detector is positioned so that a transverse section of the patient that includes the treatment target lies between opposing portions of the PET detector.

A method and apparatus are provided for positron emission imaging to correct a position at which a gamma ray was detected, when the gamma ray is scattered during detection. When Compton scattering occurs during detection of a gamma ray, the energy of the gamma ray deposited in multiple crystals in an array of detector elements. The corrected position is determined as a weighted sum of the position of the multiple crystals, each weighted by an inverse of the energy measured at the respective crystal. Further, the inverse-energy weight can be raised to a power p. A minimum energy threshold can be applied to determine the multiple crystals at which the gamma ray energy is deposited. The corrected position can be a floating position or can be rounded to a nearest crystal or to a nearest virtual sub-crystal.

A method and an apparatus for distinguishing radionuclides are disclosed. The method comprises the steps of: receiving energy generated in one or more radioactive elements; applying energy as a weight for each channel to spectrum of the received energy; and distinguishing the one or more radioactive elements on the basis of the spectrum of the spectrum to which the weight is applied. A radioactive element having an energy value corresponding to a peak value of the spectrum of the energy to which the weight is applied, as an energy value of a Compton edge, is distinguished as the one or more radioactive elements. According to the present invention, it is possible to more accurately monitor radiation even while using a plastic scintillator, and further to improve energy resolution of a plastic scintillator.