Abstract: A distributed data collection architecture for a PET system includes a plurality of data collection boards, wherein each data collection board is coupled to a respective gantry segment of the PET system. The PET system includes a modular gantry having a plurality of gantry segments that are physically separate from each other, and each gantry segment includes a plurality of detector modules coupled to a respective data collection board. Each respective data collection board is configured to acquire all detector event data from a respective plurality of detector modules of the respective gantry segment the respective data collection board is coupled to. Only one data collection board of the plurality of data collection boards is configured to act as a master data collection board that collects all of the detector event data from each data collection board and to generate coincidence pairs from all of the detector event data.

Abstract: A radiation detector assembly is provided that includes a semiconductor detector having a surface, plural pixelated anodes, and at least one processor. The pixelated anodes are disposed on the surface. Each pixelated anode is configured to generate a primary signal responsive to reception of a photon by the pixelated anode and to generate at least one secondary signal responsive to an induced charge caused by reception of a photon by at least one adjacent anode. The at least one processor is operably coupled to the pixelated anodes. The at least one processor configured to define sub-pixels for each pixelated anode; acquire signals corresponding to acquisition events from the pixelated anodes; determine sub-pixel locations for the acquisition events using the signals; and apply at least one calibration parameter on a per sub-pixel basis for the acquisition events based on the determined sub-pixel locations.

Abstract: A radiation detector assembly is provided that includes a semiconductor detector having a surface, plural pixelated anodes, and at least one processor. The pixelated anodes are disposed on the surface. Each pixelated anode is configured to generate a primary signal responsive to reception of a photon by the pixelated anode and to generate at least one secondary signal responsive to an induced charge caused by reception of a photon by at least one adjacent anode. The at least one processor is operably coupled to the pixelated anodes. The at least one processor configured to define sub-pixels for each pixelated anode; acquire signals corresponding to acquisition events from the pixelated anodes; determine sub-pixel locations for the acquisition events using the signals; and apply at least one calibration parameter on a per sub-pixel basis for the acquisition events based on the determined sub-pixel locations.

Abstract: A radiation detection system includes a detector unit and at least one processor. The detector unit is configured to generate signals responsive to radiation. The at least one processor is operably coupled to the detector unit and configured to receive the signals from the detector unit. The at least one processor is configured to obtain, during an imaging process, a first count for at least one of the signals corresponding to a first intrinsic energy window, the first energy window corresponding to values higher than an intrinsic peak value; obtain a second count for the at least one of the signals corresponding to a second intrinsic energy window, the second energy window corresponding to values lower than the intrinsic peak value; and adjust a gain applied to the signals based on at least the first count and the second count.

Abstract: A radiation detector assembly is provided including a semiconductor detector, pixelated anodes, and at least one processor. The pixelated anodes are disposed on a surface of the semiconductor detector, and configured to generate a primary signal responsive to reception of a photon and a secondary signal responsive to an induced charge caused by reception of a photon by at least one adjacent anode. The at least one processor is operably coupled to the pixelated anodes, and configured to define sub-pixels for each pixelated anode; acquire primary signals and secondary signals from the pixelated anodes; determine sub-pixel locations for acquisition events using the primary and secondary signals; generate a sub-pixel energy spectrum for each sub-pixel; apply at least one energy calibration parameter to adjust the sub-pixel energy spectra for each pixelated anode; and, for each pixelated anode, combine the adjusted sub-pixel energy spectra to provide a pixelated anode spectrum.

Abstract: A radiation detection system includes a detector unit and at least one processor. The detector unit is configured to generate signals responsive to radiation. The at least one processor is operably coupled to the detector unit and configured to receive the signals from the detector unit. The at least one processor is configured to obtain, during an imaging process, a first count for at least one of the signals corresponding to a first intrinsic energy window, the first energy window corresponding to values higher than an intrinsic peak value; obtain a second count for the at least one of the signals corresponding to a second intrinsic energy window, the second energy window corresponding to values lower than the intrinsic peak value; and adjust a gain applied to the signals based on at least the first count and the second count.

Abstract: A radiation detection system includes a detector unit and at least one processor. The detector unit is configured to generate signals responsive to radiation events. The at least one processor receives the signals, and is configured to obtain a first count for at least one of the signals corresponding to a first energy window, the first energy window corresponding to values higher than a nominal peak value; obtain a second count for the at least one of the signals corresponding to a second energy window, the second energy window corresponding to values lower than the nominal peak value; obtain at least one auxiliary count for the at least one of the signals corresponding to at least one auxiliary energy window; and adjust a gain applied to the signals based on the first count, the second count, and the at least one auxiliary count.

Abstract: A radiation detector assembly is provided including a semiconductor detector, pixelated anodes, and at least one processor. The pixelated anodes are disposed on a surface of the semiconductor detector, and configured to generate a primary signal responsive to reception of a photon and a secondary signal responsive to an induced charge caused by reception of a photon by at least one adjacent anode. The at least one processor is operably coupled to the pixelated anodes, and configured to define sub-pixels for each pixelated anode; acquire primary signals and secondary signals from the pixelated anodes; determine sub-pixel locations for acquisition events using the primary and secondary signals; generate a sub-pixel energy spectrum for each sub-pixel; apply at least one energy calibration parameter to adjust the sub-pixel energy spectra for each pixelated anode; and, for each pixelated anode, combine the adjusted sub-pixel energy spectra to provide a pixelated anode spectrum.

Abstract: A multiplexing circuit for a positron emission tomography (PET) detector includes a delay circuit and a multiplexer communicating with the delay circuit. The delay circuit configured to receive a plurality of timing pickoff (TPO) signals from a plurality of positron emission tomography (PET) detector units, add a delay time to at least one of the plurality of TPO signals, and transmit the TPO signals based on the delay time to the multiplexer, the multiplexer configured to a multiplex the TPO signals and output a single TPO signal from the plurality of TPO signals to a Time-to-Digital Convertor (TDC). A method of operating a multiplexer and a imaging system including a multiplexer are also provided.

Abstract: A multiplexing circuit for a positron emission tomography (PET) detector includes a delay circuit and a multiplexer communicating with the delay circuit. The delay circuit configured to receive a plurality of timing pickoff (TPO) signals from a plurality of positron emission tomography (PET) detector units, add a delay time to at least one of the plurality of TPO signals, and transmit the TPO signals based on the delay time to the multiplexer, the multiplexer configured to a multiplex the TPO signals and output a single TPO signal from the plurality of TPO signals to a Time-to-Digital Convertor (TDC). A method of operating a multiplexer and a imaging system including a multiplexer are also provided.

Abstract: A timing circuit that includes a first serializer/deserializer (SERDES) configured to receive a parallel rate clock signal and a system clock start signal from an imaging system and generate a first output, a second SERDES configured to receive a stop signal that is based on an output from the medical imaging system and generate a second output, and a timestamp calculator configured to utilize the first and second outputs to generate a timestamp. A medical imaging system and a method of operating a timing circuit are also described.

Abstract: A method of correcting a timing signal that represents an arrival time of a photon at a positron emission tomography (PET) detector includes receiving a timing signal that represents an arrival time of a photon at a PET detector, receiving an energy signal indicative of an energy of the photon, calculating a timing correction using the energy signal, modifying the timing signal using the timing correction, and generating an image of an object using the modified timing signal. A system and non-transitory computer readable medium are also described herein.

Abstract: A timing circuit that includes a first serializer/deserializer (SERDES) configured to receive a parallel rate clock signal and a system clock start signal from an imaging system and generate a first output, a second SERDES configured to receive a stop signal that is based on an output from the medical imaging system and generate a second output, and a timestamp calculator configured to utilize the first and second outputs to generate a timestamp. A medical imaging system and a method of operating a timing circuit are also described.

Abstract: A method of correcting a timing signal that represents an arrival time of a photon at a positron emission tomography (PET) detector includes receiving a timing signal that represents an arrival time of a photon at a PET detector, receiving an energy signal indicative of an energy of the photon, calculating a timing correction using the energy signal, modifying the timing signal using the timing correction, and generating an image of an object using the modified timing signal. A system and non-transitory computer readable medium are also described herein.

Abstract: A timing circuit for implementation in a medical imaging system such as a PET scanner, and a method of ascribing times to events in such systems, is disclosed. In one embodiment, the timing circuit includes an n-phase clock having n frequencies of operation, wherein the clock is selectable to provide n-signals that each vary at n frequencies, an n-phase counter including n counter elements coupled to the clock, an n-phase status detection circuit including n status circuits coupled to the n-phase clock, and an n-phase output circuit including n-registers coupled to the n-phase clock and respectively coupled to the n-phase counter and to n-phase status detection circuit, wherein n-registers respectively receive the n-clock signals, the n-count signals, and the n-status signals, respectively, and in response respectively provide n-output signals that collectively form an output signal indicative of a time at which the event detection signal experienced the first status change.

Abstract: The present invention, in one form, is a communication system for transmitting high-speed data across an imaging system slip-ring. In one embodiment, the communication system includes a transmitter and a receiver. The transmitter generates encoded serial data that is transmitted across the slip-ring 1 bit at a time to the receiver. The encoded data includes command codes, message blocks having CRC data, and SYNC data. Using the commands codes, the receiver decodes the data into byte data. The receiver utilizes the CRC data to detect and correct errors in the transmitted data and the SYNC data to synchronize the receiver with the transmitter.