Abstract: A method for improving timing response in light-sharing scintillation detectors is disclosed. The method includes detecting an event, by a plurality of photo sensors, from a scintillation crystal. The method then includes sampling and digitizing the photo sensor outputs by an analog-to-digital converter. Then the method includes correcting associated timing data, by a processor, for each of the photo sensor outputs based on a lookup table. The method then includes selectively time shifting the photo sensor outputs based on the lookup table to generate corrected photo sensor outputs. The method then includes summing the corrected photo sensor outputs by the processor. The method then includes generating an event time, by the processor, for the detected event based on the sum of the corrected photo sensor outputs.

Abstract: A method for improving timing response in light-sharing scintillation detectors is disclosed. The method includes detecting an event, by a plurality of photo sensors, from a scintillation crystal. The method then includes sampling and digitizing the photo sensor outputs by an analog-to-digital converter. Then the method includes correcting associated timing data, by a processor, for each of the photo sensor outputs based on a lookup table. The method then includes selectively time shifting the photo sensor outputs based on the lookup table to generate corrected photo sensor outputs. The method then includes summing the corrected photo sensor outputs by the processor. The method then includes generating an event time, by the processor, for the detected event based on the sum of the corrected photo sensor outputs.

Abstract: A method, disclosure relates to for improving detection of true coincidence events and differentiating them from events detected from scattered and random gamma photons, comprises receiving electromagnetic radiation at a plurality of photo detectors that was generated by a scintillating crystal impacted by a gamma photon, and processing data received at a subset of the plurality of photo detectors that are closer to a scintillating crystal, thereby improving a timing coincidence window for detecting a coincidence event.

Abstract: A data processing process and embodiment for optimizing the signal path for multi-modality imaging is described. The embodiment and process optimizes the signal to noise ratio in a positron emission tomography (PET) signal path utilizing scintillation crystals, avalanche photo diodes, and charge sensitive preamplifiers in a dual modality MRI/PET scanner. The dual use of both and analog pole zero circuit and a digital filter enables higher signal levels or a fixed ADC input range and thus a higher possible signal to noise ratio in the presence of significant pileup caused by high positron activity. The higher signal to noise ratio is needed in the PET signal architecture, because of the presence of non-modal time varying electromagnetic fields from the MR, which are a significant source of noise for the wideband PET signal modality.

Abstract: A method for improving timing response in light-sharing scintillation detectors is disclosed. The method includes detecting an event, by a plurality of photo sensors, from a scintillation crystal. The method then includes sampling and digitizing the photo sensor outputs by an analog-to-digital converter. Then the method includes correcting associated timing data, by a processor, for each of the photo sensor outputs based on a lookup table. The method then includes selectively time shifting the photo sensor outputs based on the lookup table to generate corrected photo sensor outputs. The method then includes summing the corrected photo sensor outputs by the processor. The method then includes generating an event time, by the processor, for the detected event based on the sum of the corrected photo sensor outputs.

Abstract: A Positron Emission Tomography (PET) scanner has a plurality of photo detector blocks. Each photo detector block or region has a plurality of photo detectors, a multiplexer receiving output signals from the plurality of photo detectors and generating a multiplexer output signal, a multiplexer control unit controlling switching of the multiplexer, and an analog-to-digital converter receiving the multiplexer output signal and generating a digital output signal.

Abstract: A method for improving timing response in light-sharing scintillation detectors is disclosed. The method includes detecting an event, by a plurality of photo sensors, from a scintillation crystal. The method then includes sampling and digitizing the photo sensor outputs by an analog-to-digital converter. Then the method includes correcting associated timing data, by a processor, for each of the photo sensor outputs based on a lookup table. The method then includes selectively time shifting the photo sensor outputs based on the lookup table to generate corrected photo sensor outputs. The method then includes summing the corrected photo sensor outputs by the processor. The method then includes generating an event time, by the processor, for the detected event based on the sum of the corrected photo sensor outputs.

Abstract: A method, process and apparatus for improved nuclear imaging. Specifically, the disclosure relates to improving detection of true coincidence events and differentiating them from events detected from scattered and random gamma photons. Embodiments comprise receiving electromagnetic radiation at a plurality of photo detectors that was generated by a scintillating crystal impacted by a gamma photon. Embodiments further comprise processing data received at a subset of the plurality of photo detectors that are closer to a scintillating crystal, thereby improving a timing coincidence window for detecting a coincidence event.

Abstract: A data processing process and embodiment for optimizing the signal path for multi-modality imaging is described. The embodiment and process optimizes the signal to noise ratio in a positron emission tomography (PET) signal path utilizing scintillation crystals, avalanche photo diodes, and charge sensitive preamplifiers in a dual modality MRI/PET scanner. The dual use of both and analog pole zero circuit and a digital filter enables higher signal levels or a fixed ADC input range and thus a higher possible signal to noise ratio in the presence of significant pileup caused by high positron activity. The higher signal to noise ratio is needed in the PET signal architecture, because of the presence of non-modal time varying electromagnetic fields from the MR, which are a significant source of noise for the wideband PET signal modality.

Abstract: A constant fraction discriminating circuit outputs timing information corresponding to an event corresponding to a detected photon for providing nuclear medicine imaging. The constant fraction discriminating circuit includes a stripline or microstrip delay element.

Abstract: A Positron Emission Tomography (PET) scanner has a plurality of photo detector blocks. Each photo detector block or region has a plurality of photo detectors, a multiplexer receiving output signals from the plurality of photo detectors and generating a multiplexer output signal, a multiplexer control unit controlling switching of the multiplexer, and an analog-to-digital converter receiving the multiplexer output signal and generating a digital output signal.

Abstract: A constant fraction discriminating circuit outputs timing information corresponding to an event corresponding to a detected photon for providing nuclear medicine imaging. The constant fraction discriminating circuit includes a stripline or microstrip delay element.

Abstract: A method and apparatus for determining and correcting the baseline of a continuously sampled signal for use in positron emission tomography. The method employs continuous signal sampling to determine the signal level at time t(0) so that an accurate determination of an integrated signal may be calculated, resulting in an accurate energy estimate for an ac-coupled, continuously-sampled signal at various count rates. The device includes a front-end electronics processing channel including primarily an analog CMOS ASIC, a bank of ADCs, an FPGA-based digital sequencer, and two RAMs. The processing electronics perform continuous digital integration of PMT signals to obtain normalized position and energy. Continuous baseline restoration (BLR) is used, wherein the baseline of the signal pulses are placed at mid-scale by continuously sampling the ADC, thus always making available the past history. A correction signal is generated for use in negative feedback control of the baseline.

Abstract: A method and apparatus for determining and correcting the baseline of a continuously sampled signal for use in positron emission tomography. The method employs continuous signal sampling to determine the signal level at time t(0) so that an accurate determination of an integrated signal may be calculated, resulting in an accurate energy estimate for an ac-coupled, continuously-sampled signal at various count rates. The device includes a front-end electronics processing channel including primarily an analog CMOS ASIC, a bank of ADCs, an FPGA-based digital sequencer, and two RAMs. The processing electronics perform continuous digital integration of PMT signals to obtain normalized position and energy. Continuous baseline restoration (BLR) is used, wherein the baseline of the signal pulses are placed at mid-scale by continuously sampling the ADC, thus always making available the past history. A correction signal is generated for use in negative feedback control of the baseline.

Abstract: An apparatus and method for determining the total energy of a continuously under-sampled energy signal resulting from an annihilation event detected by a positron emission tomograph (PET) scanner. An annihilation event is detected by a scintillator crystal and photomultiplier tube, which produces an energy signal that is continuously under-sampled by an analog-to-digital converter. The start time of the energy signal is determined by a constant fraction discriminator and time-to-digital converter. The start time is used to calculate a new amplitude for each sample, from which the total energy can be calculated.

Abstract: An apparatus and method for determining the total energy of a continuously under-sampled energy signal resulting from an annihilation event detected by a positron emission tomograph (PET) scanner. An annihilation event is detected by a scintillator crystal and photomultiplier tube, which produces an energy signal that is continuously under-sampled by an analog-to-digital converter. The start time of the energy signal is determined by a constant fraction discriminator and time-to-digital converter. The start time is used to calculate a new amplitude for each sample, from which the total energy can be calculated.