Abstract: A scintillation block detector employs an array of optically air coupled scintillation pixels, the array being wrapped in reflector material and optically coupled to an array of silicon photomultiplier light sensors with common-cathode signal timing pickoff and individual anode signal position and energy determination. The design features afford an optimized combination of photopeak energy event sensitivity and timing, while reducing electronic circuit complexity and power requirements, and easing necessary fabrication methods. Four of these small blocks, or “miniblocks,” can be combined as optically and electrically separated quadrants of a larger single detector in order to recover detection efficiency that would otherwise be lost due to scattering between them.

Abstract: Provided is a method of fabricating a detector array that includes preparing a plurality of slabs of an optical medium of an imaging device, forming a plurality of optical boundaries within at least one of the slabs of optical medium, where the plurality of optical boundaries defining a 1×N array of non-contiguous, independent light-redirecting regions within the at least one slab, arranging the plurality of slabs into a stack with a reflective layer defined between each adjacent slab and affixing the positions of the plurality of slabs with respect to each other. A detector array formed using the method is also provided.

Abstract: A method is for determining a heating effect of an imaging sequence of a second imaging modality on a detector of a first modality of a combined imaging device in dependence of a reference imaging sequence of the second imaging modality. A further method is for compensating a heating effect of an imaging sequence of a second imaging modality on a detector of a first modality of a combined imaging device. Furthermore, a combined imaging device includes a magnetic resonance imaging device and a first modality including a detector and a temperature compensation unit configured to compensate for a temperature variation of the detector. The combined imaging device is configured to perform a method for determining a heating effect of an imaging sequence of the magnetic resonance imaging device on the detector of the first modality in dependence of a reference imaging sequence of the magnetic resonance imaging device.

Abstract: Systems and methods for configuring a radiation detector are provided. A first event is detected at a first scintillator crystal of a first detector unit. A second coincident event is detected at a second scintillator crystal of a second detector unit adjacent to the first detector unit. Operating parameters are calculated for the first detector unit based on the coincident events.

Abstract: Systems and methods for configuring a radiation detector are provided. A first event is detected at a first scintillator crystal of a first detector unit. A second coincident event is detected at a second scintillator crystal of a second detector unit adjacent to the first detector unit. Operating parameters are calculated for the first detector unit based on the coincident events.

Abstract: A scintillation block detector employs an array of optically air coupled scintillation pixels, the array being wrapped in reflector material and optically coupled to an array of silicon photomultiplier light sensors with common-cathode signal timing pickoff and individual anode signal position and energy determination. The design features afford an optimized combination of photopeak energy event sensitivity and timing, while reducing electronic circuit complexity and power requirements, and easing necessary fabrication methods. Four of these small blocks, or “miniblocks,” can be combined as optically and electrically separated quadrants of a larger single detector in order to recover detection efficiency that would otherwise be lost due to scattering between them.

Abstract: A scintillation block detector employs an array of optically air coupled scintillation pixels, the array being wrapped in reflector material and optically coupled to an array of silicon photomultiplier light sensors with common-cathode signal timing pickoff and individual anode signal position and energy determination. The design features afford an optimized combination of photopeak energy event sensitivity and timing, while reducing electronic circuit complexity and power requirements, and easing necessary fabrication methods. Four of these small blocks, or “miniblocks,” can be combined as optically and electrically separated quadrants of a larger single detector in order to recover detection efficiency that would otherwise be lost due to scattering between them.

Abstract: Systems and methods for configuring a radiation detector are provided. A first event is detected at a first scintillator crystal of a first detector unit. A second coincident event is detected at a second scintillator crystal of a second detector unit adjacent to the first detector unit. Operating parameters are calculated for the first detector unit based on the coincident events.

Abstract: A radiation detector comprises a first scintillator having a first peak wavelength and a second scintillator positioned on the first scintillator. The second scintillator has a second peak wavelength different from the first peak wavelength. A plurality of photon detectors are provided. The first scintillator is positioned over and contacts each of the plurality of photon detectors. The plurality of photon detectors include first detectors and second detectors. The second detectors differ from the first detectors in doping profile, pn junction depth, or front-versus-backside illumination geometry. The first detectors are more sensitive to the first peak wavelength than the second peak wavelength. The second detectors are more sensitive to the second peak wavelength than the first detectors.

Abstract: An automated blood sampling system for PET imaging applications that can be operated in or very near to the field of view (FOV) of an MR scanner, such as in a combined MR/PET imaging system. A radiation detector uses APDs (avalanche photo-diodes) to collect scintillation light from crystals in which the positron-electron annihilation photons are absorbed. The necessary gamma shielding is made from a suitable shielding material, preferably tungsten polymer composite. Because the APDs are quite small and are magnetically insensitive, they can be operated in the strong magnetic field of an MR apparatus without disturbance.

Abstract: Systems and methods for configuring a radiation detector are provided. A first event is detected at a first scintillator crystal of a first detector unit. A second coincident event is detected at a second scintillator crystal of a second detector unit adjacent to the first detector unit. Operating parameters are calculated for the first detector unit based on the coincident events.

Abstract: A scintillation block detector employs an array of optically air coupled scintillation pixels, the array being wrapped in reflector material and optically coupled to an array of silicon photomultiplier light sensors with common-cathode signal timing pickoff and individual anode signal position and energy determination. The design features afford an optimized combination of photopeak energy event sensitivity and timing, while reducing electronic circuit complexity and power requirements, and easing necessary fabrication methods. Four of these small blocks, or “miniblocks,” can be combined as optically and electrically separated quadrants of a larger single detector in order to recover detection efficiency that would otherwise be lost due to scattering between them.

Abstract: A phantom for use in quality control measurement of a fully integrated magnetic resonance/PET scanner is disclosed. The phantom features radiation activity distributed throughout an electrically conductive binder. Suitably, the binder is elastomeric and includes carbon fibers distributed throughout it to set the conductivity of the phantom to a desired level. The phantom is applicable to various multimodality integrated medical imaging systems such as MR/SPECT and MR/CT in addition to MR/PET.

Abstract: A phantom for use in quality control measurement of a fully integrated magnetic resonance/PET scanner is disclosed. The phantom features radiation activity distributed throughout an electrically conductive binder. Suitably, the binder is elastomeric and includes carbon fibers distributed throughout it to set the conductivity of the phantom to a desired level. The phantom is applicable to various multimodality integrated medical imaging systems such as MR/SPECT and MR/CT in addition to MR/PET.

Abstract: A phantom for use in generating a normalization data set to be used in PET scanning (particularly integrated MR/PET scanning) is disclosed. The phantom features radiation activity distributed throughout a foam material. The foam—e.g., a polyurethane foam—may be produced by reacting two liquids, one of which is emulsified with water in which Ge68 has been dissolved. The foam produced thereby exhibits uniform distribution of radioactivity and a long mean free path for 511 keV gamma particles—two attributes that are important attributes of a PET phantom.

Abstract: A phantom for use in generating a normalization data set to be used in PET scanning (particularly integrated MR/PET scanning) is disclosed. The phantom features radiation activity distributed throughout a foam material. The foam—e.g., a polyurethane foam—may be produced by reacting two liquids, one of which is emulsified with water in which Ge68 has been dissolved. The foam produced thereby exhibits uniform distribution of radioactivity and a long mean free path for 511 keV gamma particles—two attributes that are important attributes of a PET phantom.

Abstract: An automated blood sampling system for PET imaging applications that can be operated in or very near to the field of view (FOV) of an MR scanner, such as in a combined MR/PET imaging system. A radiation detector uses APDs (avalanche photo-diodes) to collect scintillation light from crystals in which the positron-electron annihilation photons are absorbed. The necessary gamma shielding is made from a suitable shielding material, preferably tungsten polymer composite. Because the APDs are quite small and are magnetically insensitive, they can be operated in the strong magnetic field of an MR apparatus without disturbance.