Abstract: PET/MR images are compensated with simplified adaptive algorithms for truncated parts of the body. The compensation adapts to a specific location of truncation of the body or organ in the MR image, and to attributes of the truncation in the truncated body part. Anatomical structures in a PET image that do not require any compensation are masked using a MR image with a smaller field of view. The organs that are not masked are then classified as types of anatomical structures, the orientation of the anatomical structures, and type of truncation. Structure specific algorithms are used to compensate for a truncated anatomical structure. The compensation is validated for correctness and the ROI is filled in where there is missing voxel data. Attenuation maps are generated from the compensated ROI.

Abstract: A method include obtaining at least one first PET image of a subject acquired by a PET scanner and at least one first MR image of the subject acquired by an MR scanner. The method may also include obtaining a target neural network model. The target neural network model may provide a mapping relationship between PET images, MR images, and corresponding attenuation correction data, and output attenuation correction data associated with a specific PET image of the PET images. The method may further include generating first attenuation correction data corresponding to the subject using the target neural network model based on the at least one first PET image and the at least one first MR image of the subject, and determining a target PET image of the subject based on the first attenuation correction data corresponding to the subject.

Abstract: A Positron Emission Tomography (PET) apparatus according to an embodiment includes processing circuitry. The processing circuitry is configured to obtain information about a defective channel of a PET detector at a second point in time later than a first point in time corresponding to a first sensitivity map that is a sensitivity map of the PET detector corresponding to the first point in time and being stored in a storage unit. The processing circuitry is configured to generate a second sensitivity map that is a sensitivity map of the PET detector corresponding to the second point in time, on the basis of the information about the defective channel.

Abstract: A method of controlling and processing data from a hybrid PET-MR imaging system includes acquiring a positron emission tomographic (PET) dataset over a time period, wherein the PET dataset is affected by a quasi-periodic motion of the patient, and acquiring magnetic resonance (MR) data during the time period such that the acquisition time of the MR data relative to the PET dataset is known. A characteristic of the patient motion is then determined based on the PET dataset and the MR data is processed based on the characteristic of patient motion.

Abstract: The glass-based THz optical waveguides (10) disclosed herein are used to guide optical signals having a THz frequency in the range from 0.1 THz to (10) THz and include a core (20) surrounded by a cladding (30). The core has a diameter D1 in the range from (30) ?m to 10 mm and is made of fused silica glass having a refractive index n1. The cladding is made of either a polymer or a glass or glass soot and has a refractive index n2<n1 and an outer diameter D2 in the range from 100 ?m to 12 mm. The THz optical waveguides can be formed using processes that are extensions of either fiber, ceramic and soot-based technologies. In an example, the THz waveguides have a dielectric loss Df<0.005 at 100 GHz.

Abstract: Various aspects include methods of compensating for issues caused by charge sharing between pixels in pixel radiation detectors. Various aspects may include measuring radiation energy spectra with circuitry capable of registering detection events occurring simultaneous or coincident in two or more pixels, adjusting energy measurements of simultaneous-multi-pixel detection events by a charge sharing correction factor, and determining a corrected energy spectrum by adding the adjusted energy measurements of simultaneous-multi-pixel detection events to energy spectra of detection events occurring in single pixels. Adjusting energy measurements of simultaneous-multi-pixel detection events may include multiplying measured energies of simultaneous-multi-pixel detection events by a factor of one plus the charge sharing correction factor.

Abstract: Disclosed are calibration assembly and calibration method of calibrating geometric parameters of a CT apparatus. The calibration assembly includes at least one calibration unit each including a plurality of calibration wires, and the plurality of calibration wires are arranged regularly in a same plane. The calibration assembly is easy to be processed and can be used to calibrate geometric parameters of a CT apparatus, and the calibration operations are simple and easy to be implemented.

Abstract: Various aspects include methods for compensating for the effects of charge sharing among pixelate detectors in X-ray detectors by applying a correspondence factor to counts of X-ray photons in energy bins to estimate incident X-ray photon energy bins. The correspondence factor may be determined by determining an incident X-ray photon energy spectrum, adjusting the incident X-ray photon energy spectrum to account for an energy resolution of the pixelated detector, generating a charge sharing model for the adjusted incident X-ray photon energy spectrum based on a percentage charge sharing parameter of the pixelated detector, applying the charge sharing model to energy bins of the pixelated detector to estimate counts in each of the energy bins, and determining the correspondence factor by comparing the estimated counts in each of the energy bins to counts in the energy bins that would be expected for the adjusting the incident X-ray photon energy spectrum.

Abstract: Various aspects include methods of compensating for issues caused by charge sharing between pixels in pixel radiation detectors. Various aspects may include measuring radiation energy spectra with circuitry capable of registering detection events occurring simultaneous or coincident in two or more pixels, adjusting energy measurements of simultaneous-multi-pixel detection events by a charge sharing correction factor, and determining a corrected energy spectrum by adding the adjusted energy measurements of simultaneous-multi-pixel detection events to energy spectra of detection events occurring in single pixels. Adjusting energy measurements of simultaneous-multi-pixel detection events may include multiplying measured energies of simultaneous-multi-pixel detection events by a factor of one plus the charge sharing correction factor.

Abstract: An online real-time correction method and system for a positron emission tomography (PET) detector. The method includes: acquiring a drifted channel number of a peak position of a full-energy peak in a drifted energy spectrum after a gain value of a PET detector system has changed and a ratio of a currently accumulated energy of each signal channel to a current total accumulated energy of all signal channels; substituting the above parameters, an initial channel number of the peak position of the full-energy peak in an initial energy spectrum and a ratio of an initially accumulated energy of each signal channel to a total initially accumulated energy of all of the signal channels in the PET detector system into a gain adjustment ratio calculation formula to calculate a gain adjustment ratio; and adjusting, according to the gain adjustment ratio, a gain value of the PET detector system.

Abstract: A method is for recording a region of interest of an examination object with a computed tomography system including an energy-selective X-ray detector with a number of energy threshold values that can be set by way of an energy threshold values. In an embodiment, the method includes first recording of first projection scan data with a first set of energy thresholds; setting a second set of energy thresholds different from the first set of energy thresholds, based on a temporally variable parameter; and second recording of second projection scan data different from the first projection scan data with the second set of energy thresholds.

Abstract: One embodiment provides a method, including: receiving a dataset associated with a plurality of photon emission events interacting with a detector array of an imaging device; identifying a first subset of the dataset associated with a plurality of unscattered photon emission events from the plurality of photon emission events; identifying a second subset of the dataset associated with at least one scattered photon event from the plurality of photon emission events; determining, for a scattered photon event, a likely location of emission of the scattered photon event using data from the first subset of the dataset associated with the plurality of unscattered photon events; and correcting the dataset by associating the scattered photon event with the determined likely location of emission. Other aspects are described and claimed.

Abstract: According to an embodiment, a photon counting CT apparatus includes a scintillator, a photodiode array, a holder, a divider, and an image generator. The scintillator is configured to convert X-rays into light. The array includes first and second pixels. The first pixel includes a photodiode in a first range receiving the light emitted from the scintillator. The photodiode outputs an electrical signal based on the light. The second pixel includes a photodiode in a second range different from the first range. The holder is circuitry configured to hold a value of an electrical signal output by the second pixel. The divider circuitry is configured to count the number of photons of light incident on the first pixel by dividing an integrated value of electrical signals output by the first pixel by the held value. The image generator is circuitry configured to reconstruct an image based on the counted number.

Abstract: A method comprises: detecting a plurality of radiation events using a plurality of radiation detectors; determining a fraction of the plurality of radiation events, such that a coincidence circuit has sufficient capacity to process each radiation event in the fraction of the plurality of radiation events; counting the determined fraction of the plurality of radiation events using the coincidence circuit, and excluding a remainder of the plurality of radiation events from the counting; and performing positron emission tomography (PET) processing on each radiation event in the fraction of the plurality of radiation events.

Abstract: For count loss correction, the capability of the discriminator, measured periodically, to detect an event is identified. Rather than inserting an actual event or a signal emulating an actual event for discrimination, the capability to discriminate is tested by a virtual injection. The count loss may be directly measured without causing extra actual discrimination by the discriminator. Direct measurement with virtual testing may avoid loss of accuracy due to time and use-case variation.

Abstract: A method is disclosed for creating a motion correction for PET data acquired by a PET system from a volume segment of an examination object. The method includes acquisition of MR data within the volume segment by the magnetic resonance system; and determination of a motion model of a motion within the volume segment as a function of the MR data. The motion model, as a function of a respective motion state of the motion, provides a correction specification for PET data which is acquired during this motion state. During acquisition of the MR data, specific MR data is acquired in the center of the k-space or of a straight-line segment which passes through the center of the k-space. The MR data determined is converted by a mathematical function into one value, as a function of which the respective motion state is determined.

Abstract: Methods and devices for calibrating a gain of a scintillator detector are disclosed, where a scintillation crystal of the scintillator detector includes two or more energy regions. In an example, the scintillation crystal of the scintillator detector is adopted as a radiation source for calibrating. Electric signals outputted from a rear end of the scintillator detector are collected, and actual counts of the electric signals from each of at least two energy regions of the scintillation crystal at a specified position are obtained, respectively. Then, a gain of the scintillator detector may be adjusted according to the obtained actual counts of the electric signals from the at least two energy regions.

Abstract: A self-stabilizing scintillation detector system for the measurement of nuclear radiation, preferably gamma radiation, is provided, the system comprising a scintillation crystal, a photo detector, a photomultiplier (PMT) with n dynodes and an evaluation system connected to the output port of the PMT, i.e. the anode of the PMT, the PMT comprising at least two connections to at least two different dynodes of the PMT, a device for measuring the electric current at the at least two dynodes, as well as an electronic device for determining the quotient of the measured at least two electric currents at the at least two dynodes, said quotient being a measure for the gain between the two dynodes, further comprising means for comparing the measured quotient with a reference value, and means for adjusting the gain of the PMT by utilizing the gain change over time.

Abstract: A method is provided for processing a spectrum, obtained using a particle detection system, so as to reduce spectrum artifacts arising from unresolved particle events in the detection system. An input spectrum is obtained which contains artifacts due to “pile up” in the detector. A first effect upon the input spectrum of pairs of unresolved particle events is evaluated and a first corrected input spectrum is generated which comprises the input spectrum with the first effect removed. The effect of a pairs of unresolved particle events is then evaluated for this first corrected input spectrum so as to generate a second corrected input spectrum which comprises the input spectrum with the second effect removed. An output spectrum is then generated based upon a combination of the first and second corrected input spectra. The use of the method in improving sum spectra is also discussed.

Abstract: Devices may include a scintillation detection device including a scintillator, a photon detector at least partially enclosed by the scintillator, and at least one reflector at least partially enclosing the scintillator. In another aspect, an oilfield wellbore device may include an oilfield string with at least one scintillation detection device on the string and a pressure housing enclosing the one or more scintillation detection devices. In another aspect, a method of measuring radiation in an oil and gas well may include conveying at least one scintillation detection device to at least one zone of interest in the oil and gas well and recording data from at least one scintillation detection device as a function of location in the well.

Abstract: System includes a signal processing system to receive a digital signal associated with first scintillation events and to determine a value associated with each of the events, a backend processing system to receive the values, determine an event rate based on the received values, determine whether the event rate is greater than a first threshold, and, if the event rate is greater, transmit a first instruction to increase a consecutive event dump level, and an event management control to receive the first instruction to increase the consecutive event dump level, increase the consecutive event dump level in response to the received instruction, determine a number of consecutive scintillation events of detected second scintillation events, determine to dump the consecutive scintillation events based on a comparison between the number of consecutive scintillation events and the consecutive event dump level, and transmit a second instruction to dump the consecutive scintillation events.

Abstract: An apparatus and method for determining a position of a point source arranged in a Positron Emission Tomography (PET) scanner apparatus. The apparatus includes processing circuitry configured to obtain list-mode data generated from a PET scan of the point source, determine a plurality of lines-of-response (LORs) from the obtained list-mode data, determine intersecting pairs of LORs from the determined plurality of LORs, determine corresponding coordinates of intersection points of the determined intersecting pairs of LORs, and determine the position of the point source based on the determined coordinates of the intersections points.

Abstract: An apparatus and method of processing X-ray projection data obtained using photon-counting detectors and having multiple spectral components. The processing of the projection data includes correcting for nonlinear detector response, where the detector response model includes: pileup, ballistic deficit effects, polar effects, and characteristic X-ray escape. The processing of the projection data also includes a material decomposition mapping the projection data from spectral components into material components corresponding to high-Z and low-Z materials. The material decomposition includes a noise balancing process where the allocation of spectral components between a high-energy and a low-energy combination of spectral components is adjusted such that both high- and low-energy components have signal-to-noise ratios of similar magnitude. For computed tomography (CT) applications, material decomposition can be followed by image reconstruction and then image post-processing and presentation.

Abstract: Among other things, one or more techniques and/or systems for counting detection events via a photon counting detector array is provided. A first instance where an amplitude of an electrical signal exceeds an event threshold is detected. The first instance is generated responsive to a first detection event at a detector cell. An event counter is disabled from counting other detection events at the detector cell for a first blocking interval. At a conclusion of the first blocking interval, the amplitude of the electrical signal is determined. Responsive to determining that the amplitude of the electrical signal is below the event threshold, an adjustment is made to an event count based upon the first detection event. Responsive to determining that the amplitude of the electrical signal exceeds the event threshold, the event counter is disabled from counting other detection events at the detector cell for a second blocking interval.

Abstract: A representative positron emission tomography (PET) system includes a positron emission tomography detector having one or more silicon photomultipliers that output silicon photomultipliers signals. The PET system further includes a calibration system that is electrically coupled to the silicon photomultipliers. The calibration system determines a single photoelectron response of the silicon photomultipliers signals and adjusts a gain of the silicon photomultipliers based on the single photoelectron response.

Abstract: Methods and systems for performing x-ray computerized tomographic (CT) reconstruction of imaging data on a rotatable portion of the system, such as a ring-shaped rotor. The rotor may include an x-ray source, and x-ray detector system and a processor, coupled to the detector system, for performing tomographic reconstruction of imaging data collected by the detector system.

Abstract: According to one embodiment, an X-ray computed tomography apparatus includes an X-ray tube, a detector, a first DAS, and a second DAS. The radiation detector includes a plurality of detection elements. Each detection element repeatedly detects X-rays generated by the X-ray tube and transmitted through a subject and repeatedly generates an electrical signal corresponding to the energy of the repeatedly detected X-rays. The first DAS acquires the electrical signal detected by part of the imaging region of each detection element in the integral mode. The second DAS acquires the electrical signal detected by the other part of the imaging region of each detection element in the photon count type mode.

Abstract: A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells transitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.

Abstract: A method of processing, by a processor of a computer, positron emission tomography (PET) information obtained from a PET detector, including the steps of obtaining a singles event list that includes a plurality of single event entries, each entry corresponding to a single event detected by the PET detector and including a timestamp, energy information, and crystal position information; and determining, based on the timestamp and the crystal position information of each entry and a predetermined coincidence time period, all event pairs within the plurality of single event entries, each event pair consisting of two single events whose respective timestamps differ by less than the predetermined coincidence time period, wherein the determining step determines that an event pair exists when at least two, but no more than k, single events are found within a given time window, wherein k is an integer value greater than or equal to two.

Abstract: A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells transitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.

Abstract: A method of estimating random events in positron emission tomography list mode data, including obtaining time-of-flight (TOF) list mode count data that includes TOF information; converting the obtained TOF list mode count data into four-dimensional (4D) raw sinogram count data, without using the TOF information, wherein the 4D raw sinogram count data includes random count values; interpolating the 4D raw sinogram count data to generate 4D interpolated sinogram count data; low-pass filtering the 4D interpolated sinogram count data to remove noise; converting the low-pass filtered 4D interpolated sinogram count data into filtered 4D raw sinogram count data; and generating, by a processor, five-dimensional (5D) TOF raw sinogram count data from the filtered 4D raw sinogram count data by effectively applying a TOF mask filter to the filtered 4D raw sinogram count data.

Abstract: An apparatus and method for simulating a radiation phantom so as to calibrate or measure performance of a gamma detection system. The apparatus includes a line bar configured to rotate around an axis of rotation, a source carriage configured to move linearly along the line bar and to hold an attached radiation source, and a fixture assembly configured to support the line bar, the fixture assembly being configured to attach to a patient bed.

Abstract: A process and system including a detector having a photosensor therein that outputs a signal and a plurality of after-pulse detector devices independently connected to the photosensor via respective pathways. The after-pulse detector devices each detecting an after-pulse in the signal, where the after-pulse represents an after-event in the photosensor triggered from a previous photon generating event. The system further includes a processing device that receives an indication of the detection of the after-pulse from each of the plurality of after-pulse detector devices and determines a relative delay between the respective pathways based on timing the received indications, and includes a memory that stores the relative delay in association with an identification of the corresponding after-pulse detector devices.

Abstract: A method is disclosed for recording and evaluating PET data recorded at the same time as magnetic resonance data using a combined magnetic resonance/PET apparatus, wherein in the context of a pulse sequence for recording the magnetic resonance data a magnetic resonance recording facility, including at least one gradient coil and at least one high-frequency coil, is activated. In at least one embodiment, the method includes recording the PET data and assigning the recorded PET data after the recording time point to at least two data groups assigned to a predetermined operating state of the magnetic resonance recording facility; for each data group, determining a measure of similarity of the PET data contained therein to the PET data as a whole and/or to PET data of at least one further data group, whereby if the measure of similarity is below a threshold value, the PET data of the data group is rejected and/or further evaluated separately.

Abstract: A mobile PET imager and method for the same is provided. The mobile PET imager includes a plurality of detector modules forming a ring detector, each for nuclear radiation detection. The imager may include a plurality of attenuation source housings including sources for attenuation such that each attenuation source housing is placed between two of the detector modules. A plurality of channel cards for processing data from the plurality of detector modules may be in the imager so that each channel card is shared by more than one of the detector modules. The imager may include at least one channel card for processing data from the detector modules and at least one resistor network acting as preamplifier, coupling to the detector modules and the channel card such that the channel card is mounted on the detector module in layer.

Abstract: A radiation diagnosis apparatus, which employs a reduced number of data acquisition units while showing the same effect as that of the related art (PET, SPECT or x-ray CT) includes: a first radiation detector; a second radiation detector an inverter formed at an output terminal of the first radiation detector; a discriminator for receiving a common signal from the first and second radiation detector and outputting a control signal corresponding to the input common signal; and a data acquisition unit and indentifying an output signal of which detector of the first and second detectors the input signal is according to a polarity difference of the input signal, to provide a radiation diagnosis apparatus which employs a reduced number of data acquisition units while showing the same effect as that of the related art.

Abstract: In a method of count correction for pixels of a pixilated photon counting detector, the average count value output by each of a plurality of pixels during a period of time is determined. A product is determined of the actual average count value and a multiplying correction factor. A corrected count value is then determined for the pixel equal to a sum of the product and an additive correction factor. The multiplying correction factor equals a square root of a quotient of a desired average count value to be output by each of the plurality of pixels during the period of time divided by the actual average count value. The additive correction factor equals a product of the multiplying correction factor and the actual average count value subtracted from the desired average count value.

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: The present invention provides a method for identifying and sorting sensing signals with respect to crystal locations of a scintillation detector, comprising steps of: (a) providing a crystal map detected by a crystal array, the crystal map having a plurality of peak points, each being represented by a coordinate location; (b) finding a basis point with respect to a specific area enclosing an amount of the peak points within the crystal map; (c) determining the peak point within the specific area having the shortest distance to the basis point, the peak point corresponding to a crystal element of the crystal array; (d) changing the location of the specific area; and (e) repeating steps (b) to (d) for a plurality of times to find all the crystal elements with respect to the peak points respectively.

Abstract: According to one embodiment, a nuclear medicine diagnosis includes a light signal generating unit, photodetection unit, measurement unit, calculation unit, and storage unit. The light signal generating unit repeatedly generates light signals. The photodetection unit repeatedly generates first output signals corresponding to intensities of the light signals, repeatedly generates second output signals corresponding to intensities of gamma rays emitted from a subject. The measurement unit repeatedly measures light signal detection times and repeatedly measures gamma ray detection times. The calculation unit calculates a difference between a target gamma ray detection time and a target light signal detection time of the light signal detection times for each of the gamma ray detection times. The target light signal detection time is measured before the target gamma ray detection time. The storage unit stores the calculated difference in association with a target second output signal of the second output signals.

Abstract: A radiation detecting apparatus of this invention includes an arithmetic processing device which carries out arithmetic processes for drawing boundaries based on peaks of signal strengths and separating respective positions by the boundaries, and for determining, by using spatial periodicity of the peaks, the number of peaks having failed to be separated, with a plurality of peaks connecting to each other. If the separation fails with a plurality of peaks connecting to each other, the number of peaks in error is determined using spatial periodicity of the peaks. Thus, by using spatial periodicity of the peaks, the number of peaks in error can be determined and boundaries can be set easily. As a result, incident positions can also be discriminated easily, and detecting positions of radiation can be determined easily.

Abstract: The present disclosure relates to the correction of charge loss in a radiation detector. In one embodiment, correction factors for charge loss may be determined based on depth of interaction and lateral position within a radiation detector of a charge creating event. The correction factors may be applied to subsequently measured signals to correct for the occurrence of charge loss in the measured signals.

Abstract: A method of imaging a region of interest (ROI) in an object, the ROI having an axial extent greater than an axial FOV of a PET scanner. The method includes determining a number of overlapping scans of the PET scanner necessary to image at least the axial extent of the ROI, wherein each scan has a same axial length equal to the axial FOV, and each scan overlaps an adjacent scan by a predetermined overlap percentage of the axial length of each scan. The method includes determining a total amount of excess scanning length of the scans based on the number, the axial extent of the ROI, and the axial FOV, and determining a new overlap percentage so that a new total amount of excess scanning length is zero.

Abstract: Methods and systems for calibrating a nuclear medicine imaging system are provided. One method includes acquiring spatially determined non-uniform radiation flux information from a calibration scan of a calibration source using a gamma camera having an attached non-parallel-hole collimator. The method further includes determining a measured non-uniform count density profile from the acquired non-uniform radiation flux information. The method also includes creating a gamma camera uniformity correction map derived from (i) the measured non-uniform count density profile and (ii) a modeled or calculated non-uniform count density profile for calibrating the NM imaging system.

Abstract: Systems and methods for calibrating a nuclear medicine (NM) imaging system are provided that include an NM calibration source. The NM calibration source includes an isotope source having an energy spectrum with at least one energy peak and a fluorescence layer adjacent the isotope source creating at least one additional energy peak in the energy spectrum.

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 digital photosensor that includes a photomultiplier tube (PMT) including a power distribution circuit, the PMT outputting an analog signal in response to received light; an analog-to-digital converter (ADC) to receive the analog signal and to generate a digital signal; and a non-transitory memory storing manufacturing parameters of the PMT and operational parameters of the PMT, the operational parameters being calculated by a parameter calculation unit during operation of the PMT, wherein the PMT, the ADC, and the memory are integrated into a single housing.

Abstract: Example embodiments are directed to a method of correcting attenuation in a magnetic resonance (MR) scanner and a positron emission tomography (PET) unit. The method includes acquiring PET sinogram data of an object within a field of view of the PET unit. The method further includes producing an attenuation map based on a maximum likelihood expectation maximization (MLEM) of a parameterized model instance and the PET sinogram data.

Abstract: A system and method for determining correction factors used to determine energy of an event detected by a gamma ray detector having nonlinear photosensors arranged over a scintillation array of crystal elements, the gamma ray detector using optical multiplexing or analog electronic multiplexing. The method includes acquiring, for each nonlinear photosensor, a signal value generated by the nonlinear photosensor in response to receiving scintillation light emitted by a crystal in the array of crystal elements in response to arrival of a gamma ray; and determining a relative position of the event, the relative position being one of a predetermined number of cell locations, the predetermined number of cell locations being greater than a number of crystal elements in the array of crystal elements; and determining, for each cell location, a correction factor based on an average total signal value and a predetermined energy value of the gamma ray.

Abstract: There are provided an apparatus capable of complying with arbitrary data acquisition period (frame rate) change instruction without increasing load and cost, and a method and a system for controlling such an apparatus. To realize this, in the present invention, there are included an area sensor for reading out an electric signal accumulated in a plurality of pixels arranged in a matrix, line by line, and a control unit for controlling the area sensor. The area sensor operates in a first operation for deriving radiation image data by reading during irradiation with radiation, and a second operation for deriving the radiation image data by reading during non-irradiation with radiation, alternately. The control unit switches a period for deriving the radiation image data during a time period from an end of the reading in the first operation until an end of the reading in the second operation.