Abstract: TOF-PET detector systems, and methods for imaging photon-emitting samples using the detector systems, are provided. The TOF-PET detector systems use large-area photodetectors with extremely high time-resolution and an approach to data collection and analysis that allows for the use of inexpensive low-density scintillator materials. The TOF-PET detector systems are characterized by their ability to identify, on a statistical basis, the transverse and depth location of the first of the series of energy deposition events that are generated when a gamma photon enters the low-density scintillator material.

Abstract: An X-ray therapy system includes a gantry, a positron emission tomography (PET) detection device in the gantry, and an irradiation unit in the gantry (and configured to radiate X-rays to a patient. The PET detection device has a pair of photon detection units and photon detection unit-moving devices configured to move the pair of photon detection units with respect to the gantry.

Abstract: Sensitivity correction for multiple ? radiation detectors is performed by use of sensitivity coefficients obtained through a first sensitivity coefficient calculation step for obtaining sensitivity coefficients, classified according to sensitivity factors, on the basis of coincidence counting data collected as a result of detection of ? radiation emitted from a rotated rod-shaped calibration radiation source, and through a third sensitivity coefficient calculation step for obtaining sensitivity coefficients derived from a geometrical arrangement on the basis of coincidence counting data collected in a state where arrangement of the ? radiation detectors is changed. A re-constructed image is obtained on the basis of data acquired after the sensitivity correction is finished.

Abstract: A positron emission tomography (PET) apparatus and method employs a plurality of radiation detectors (20) disposed around an imaging region (16) and configured to detect 511 keV radiation events emanating from the imaging region. A calibration phantom is disposed in the imaging region. One or more processors are configured to: acquire and store listmode data of the phantom; measure a random rate for each line of response (LOR) from the listmode data using a coincident 511 keV events detector (34) with a time offset (54); determine a singles rate for each detector pixel from the random event rate, for example via a histogram plotting singles rate for each detector pixel; compute a live time factor of each LOR; compute a dead time correction factor as the reciprocal of the live time factor; and correct images according to the dead time correction factor.

Abstract: A medical image diagnostic device according to an embodiment includes a first collector, a second collector, and an image generator. The first collector collects data from a first region of a subject through a first detector. The second collector collects data from a second region of the subject that is different from the first region through a second detector. The image generator generates a first diagnostic image from the data collected by the first collector and generates a second diagnostic image from the data collected by the second collector.

Abstract: The present disclosure relates to increasing the spatial resolution of a clinical positron emission tomography (PET) scanner. The spatial resolution of the clinical PET scanner can be increased by placing a collimator, including a plurality of pinholes, inside the clinical PET scanner. Coincidence data of the annihilation photons are acquired by the PET scanner. A computer associates a pinhole location with the two detected locations of the coincident photons. All three locations are then used in the reconstruction of a high-resolution PET image.

Abstract: A scintillation crystal can include Ln(1-y)REyX3, wherein Ln represents a rare earth element, RE represents a different rare earth element, y has a value in a range of 0 to 1, and X represents a halogen. In an embodiment, RE is Ce, and the scintillation crystal is doped with Sr, Ba, or a mixture thereof at a concentration of at least approximately 0.0002 wt. %. In another embodiment, the scintillation crystal can have unexpectedly improved linearity and unexpectedly improved energy resolution properties. In a further embodiment, a radiation detection system can include the scintillation crystal, a photosensor, and an electronics device. Such a radiation detection system can be useful in a variety of radiation imaging applications.

Abstract: A device for sensing, locating, and characterizing a radiation emitting source, including: a detection crystal having dimensions great enough such that regional differences in radiation response are generated in the detection crystal by radiation impinging on one or more surfaces of the detection crystal; and a plurality of detectors one or more of coupled to and disposed on a plurality of surfaces of the detection crystal operable for detecting the regional differences in radiation response generated in the detection crystal by the radiation impinging on the one or more surfaces of the detection crystal.

Abstract: A detector device for determining a position of reaction of gamma quanta, the device comprising: a detection layer comprising: at least one polymeric or inorganic scintillator (12, 22) for absorbing gamma quanta and for emitting and propagating scintillation photons; and photoelectric converters (14,24) for converting light signals of the scintillation photons into electric signals; and at least one additional layer comprising: strips of material (13, 23) for absorbing the scintillation photons and for emitting and propagating secondary photons; and photoelectric converters (15, 25) for converting the light signals for the scintillation photons into electric signals.

Abstract: The present invention is directed to an interrogator, method of discerning metal and radio frequency identification (RFID) objects, and an interrogation system employing the same. In one embodiment, the interrogator includes a metal sensing subsystem configured to provide a first signal having a signature representing a presence of a metal object, and a RFID sensing subsystem configured to provide a second signal having a signature representing a presence of a RFID object. The interrogator also includes a control and processing subsystem configured to discern a presence of at least one of the metal and RFID objects from one of the first and second signals.

Abstract: A detector of an embodiment includes a plurality of photomultipliers, a signal line, and identifying circuitry. The photomultipliers each convert light converted from radiation into an electric signal and output the electric signal. The signal line has a first path and a second path through which the electric signal passes and that have different lengths for each of the photomultipliers. The identifying circuitry identifies the photomultiplier that outputs the electric signal by a time difference between the electric signal passing through the first path and the electric signal passing through the second path.

Abstract: A positron emission tomography (PET) data processing method comprises obtaining PET data from a PET detector, wherein the PET detector comprises an array of detector elements, and wherein the PET data is representative of a PET measurement of at least part of a subject. The method comprises identifying in the PET data a plurality of paired events, wherein each paired event comprises a first photon event in a first region of the PET detector and a second photon event in a second region of the PET detector. The first photon event comprises an energy deposition in a first detector element of the array or in a first detection region of the first detector element due to a scattering of a first photon at a first azimuthal scattering angle and an associated energy deposition by the scattered first photon in a second detector element of the array or in a second detection region of the first detector element or of the second detector element.

Abstract: A molecular breast imaging (MBI) unit includes a housing, a first detector unit, and a second detector unit. The housing is configured to be positioned in an imaging position for imaging an object. The first detector unit includes a first nuclear medicine (NM) imaging detector secured in the housing. The first detector unit is configured to acquire first imaging information of the object when the housing is in the imaging position. The second detector unit includes a second NM imaging detector secured in the housing. The second detector unit is configured to acquire second imaging information of the object when the housing is in the imaging position. The housing includes an opening disposed between the first and second detector units. The opening is configured to allow access by a biopsy assembly to the object with the housing in the imaging position.

Abstract: Disclosed is a multi-channel light measurement system adapted to illuminate and measure a test sample in a vessel. The multi-channel light measurement system has at least one photodetector per channel and a variable integrate and hold circuit coupled to each photodetector, the variable integrate and hold circuit allows adjustment of a sampling factor selected from a group of an integration time, a value of capacitance, an area of a discrete photodetector array, or any combination thereof. The system may readily equilibrate reference intensity output for multiple channels. Methods and apparatus are disclosed, as are other aspects.

Abstract: A Compton camera includes a scattering detection unit, an absorption detection unit, a signal processing unit, a first shield unit, and a second shield unit. The scattering detection unit detects Compton scattering of incident radiation emitted from a radiation source. The absorption detection unit detects absorption of incident radiation that has undergone Compton scattering at the scattering detection unit. The signal processing unit obtains an image of the radiation source based on coincident detection events of Compton scattering of radiation at the scattering detection unit and absorption of radiation at the absorption detection unit. The first and second shield units are provided between the scattering detection unit and the absorption detection unit. The first shield unit selectively allows forward-scattered radiation to pass and selectively blocks back-scattered radiation.

Abstract: A layered three-dimensional radiation position detector includes two-dimensional scintillator arrays that are pixelated by optically discontinuous surfaces and stacked on a light receiving surface of a light receiving element, responses of scintillator elements detecting radiations being made identifiable on the light receiving surface to obtain a three-dimensional radiation detection position. A scintillator array lying on a radiation incident surface side has a pixel pitch smaller than that of a scintillator array lying on a light receiving element side so that the scintillator array on the radiation incident surface side has increased resolution. A layered three-dimensional radiation position detector achieving both low cost and high resolution can thus be provided.

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 method for digitalizing a scintillation pulse may include: S1, acquiring a pulse database outputted by a detector irradiated by rays of different energy; S2, sampling and 5 quantizing each of pulses in the pulse database obtained in S1 to acquire complete energy information comprised in the pulse, S3, undersampling and quantizing each of the pulses in the pulse database obtained in step S1, and estimating or fitting energy information by using pulse prior information; S4, with the energy information obtained in S2 as a standard, determining a mapping relationship between 10 the energy information obtained by a prior information-based undersampling pulse energy acquisition method and the energy information obtained by the method of S2; and S5 correcting the energy information obtained by the prior information-based undersampling pulse energy acquisition method by using the energy mapping relationship obtained in S4.

Abstract: A rotor of a computed tomography apparatus has a rotatable mechanical support frame for mechanical retention of electrical components and electrical connection elements for electrical connection with electrical components of the computed tomography apparatus, with the electrical connection elements arranged in at least one backplane bus. A rotating unit and a computed tomography apparatus embody such a rotor.

Abstract: According to one embodiment, a medical imaging diagnosis apparatus includes a top-plate, a bed, a first gantry, a second gantry and a moving assembly. The top-plate places a subject thereon. The bed supports the top-plate. The first gantry includes an X-ray generator and an X-ray detector which revolve around the top-plate. The second gantry includes a gamma ray detector which detects gamma rays emitted from the subject. The moving assembly moves, based on a first position indicative of a center position of an effective view field in the first gantry and a second position indicative of a center position of an effective view field in the second gantry, the top-plate relative to the second position.

Abstract: This disclosure provides a method for manufacturing a large-version light guide sheet using a mask plate. The method includes adopting a mask plate containing a plurality of regions, performing selective polymerization on a photopolymerizable material mixture which is coated on a large-version light guide substrate (401) by means of the mask plate, and forming a raised or depressed microstructure (402) on the large-version light guide substrate (401), so as to constitute a large-version light guide sheet. The large-version light guide sheet comprises a plurality of units (U11, U12, U13, U14). By dividing the large-version light guide sheet, a plurality of discrete unit light guide sheets that are used for an LCD backlight source and an LED lighting assembly are obtained. The method overcomes the limitations of ink jet printing, injection molding, laser etching and other technologies, and improves the production rate of high-performance thinned light guide sheets.

Abstract: A method including accessing image data representing tissue and identifying one or more features of the tissue indicated by the image data. A model is selected for the tissue based on the one or more identified features. The image data is segmented and, using the model, one or more anatomical landmarks of the tissue indicated by the segmented image data are identified.

Abstract: An apparatus comprising a radiation source, coincident positron emission detectors configured to detect coincident positron annihilation emissions originating within a coordinate system, and a controller coupled to the radiation source and the coincident positron emission detectors, the controller configured to identify coincident positron annihilation emission paths intersecting one or more volumes in the coordinate system and align the radiation source along an identified coincident positron annihilation emission path.

Abstract: A method compensates for image artifacts in a first imaging device for imaging a first subregion of a body. The image artifacts are caused by a second subregion of the body being disposed outside of a first field of view for the first device. First measured data for the first field of view is acquired by the first device. The first subregion lies in the first field of view. Second measured data are acquired for a second field of view in a second imaging device. Image data representing the subregions in the second device are calculated from the second measured data. A model representing the subregions is calibrated using the calculated image data. The data representing the second subregion in the first device are simulated using a calibrated model. A correction of the first measured data is performed using simulated data for reducing the image artifacts.

Abstract: Anatomic range planning is provided in positron emission tomography (PET). The user indicates one or more ranges on an image of a patient based on anatomy. Rather than planning by bed position, the planning is based on the anatomy of the patient without reference to the length of the PET detector. The user interface for PET examination avoids overlapping boxes and other confusion based on bed position. Different anatomical ranges may be assigned different PET parameters, such as reconstruction parameters. A processor may automatically alter the examination (e.g., by extending the detection range beyond the region of interest or by increasing duration at an end position) to account for the sensitivity profile since the anatomical region of interest is known. Anatomical region specific directions may be included as part of planning, aiding in performing different protocols for different anatomical ranges.

Abstract: A method for determining parameters of a reaction of a gamma quantum within a scintillator of a PET scanner, comprising transforming a signal measured in the scintillator using at least one converter into an electric measurement signal, wherein the method comprises the steps of: obtaining access to a reference parameters memory (10) comprising reference signals represented in a time-voltage (Wt-v) coordinate system and in a time-amplitude fraction (Wt-f) coordinate system and having associated reaction parameters; sampling the electric measurement signal (S) measured in the time-voltage (PT-V) coordinate system and in the time-amplitude fraction (Pt-f) coordinate system; comparing results of the sampling (PT-V, PM) of the electric measurement signal (S) with the reference signals (Wt-V, Wt-f) and selecting reference shape parameters so that the reference (W) is best fitted to the results of the sampling (PT-V, PM) of the electric measurement signal (S); and determining the parameters of the reaction of the ga

Abstract: A scintillation crystal can include Ln(1-y)REyX3, wherein Ln represents a rare earth element, RE represents a different rare earth element, y has a value in a range of 0 to 1, and X represents a halogen. In an embodiment, RE is Ce, and the scintillation crystal is doped with Sr, Ba, or a mixture thereof at a concentration of at least approximately 0.0002 wt. %. In another embodiment, the scintillation crystal can have unexpectedly improved linearity and unexpectedly improved energy resolution properties. In a further embodiment, a radiation detection system can include the scintillation crystal, a photosensor, and an electronics device. Such a radiation detection system can be useful in a variety of radiation imaging applications.

Abstract: A method for calibration of TOF-PET detectors comprising polymeric scintillator strips and photoelectric converters, wherein cosmic radiation is used as a source of radiation, the method comprising the steps of: recording times of reactions of particles of cosmic radiation with the scintillator strips (101, 411, 421, 511, 521); determining spectra (301) of distribution of differences in the times at which pulses are recorded at ends of the scintillator strips (101, 411, 421, 511, 521) connected to photoelectric converters (102, 103, 412, 413, 422, 423, 512, 513, 522, 523); using the determined spectra (301) to determine timing synchronization constants of the photoelectric converters (102, 103, 412, 413, 422, 423, 512, 513, 522, 523), the constants being related to: delays within the electronics; speed of light propagation within the scintillator strip of the detection module; and resolution of the difference in times of the signals recorded at the ends of the module.

Abstract: A radiation imaging device capable of matter-element information acquisition and image based selection comprises: a radiation source generating radiation; at least one scattering device receiving radiation which includes radiation transmitting a subject and scattered radiation and scattering the received radiation; and an imaging device receiving the radiation which includes the radiation transmitting the subject and the scattered radiation to measure energy and positional information so as to calculate a two-dimensional image.

Abstract: A multimodal imaging apparatus (1a, 1b) including scintillator elements (31) for capturing incident gamma quanta (25, 61) and for emitting scintillation photons (26) in response to said captured gamma quanta (25, 61). Photosensitive elements (33) capture the emitted scintillation photons (26) and determine a spatial distribution of the scintillation photons. The imaging apparatus (1a, 1b) is configured to be switched between a first operation mode for detecting low energy gamma quanta and a second operation mode for detecting high energy gamma quanta. The scintillator elements are arranged to capture incident gamma quanta (25, 61) from the same area of interest (65) in both operation modes. The scintillator elements (31) include a first region with high energy scintillator elements (27) for capturing high energy gamma quanta and a second region with low energy scintillator elements (29) for capturing low energy gamma quanta.

Abstract: A nuclear imaging system includes a detector configured to detect at least one photon event. A timing signal path is electrically coupled to the detector. The timing signal path is configured to generate a timing signal indicative of a timing of the at least one photon event. An energy signal path is also electrically coupled to the detector. The energy signal path is configured to generate an energy signal indicative of an energy of the at least one photon event. A time-domain multiplexer is configured combine the timing signal and the energy signal into a compound signal.

Abstract: A tomography imaging apparatus is provided, including: a data acquisition unit configured to acquire a plurality of partial data respectively corresponding to a plurality of consecutive angular sections by performing a tomography scan on a moving object; and an image processing unit configured to measure global motion of the object and motion of a first region in the object based on the plurality of partial data, acquire first information representing motion of the object by reflecting the global motion in the motion of the first region, and reconstruct a final tomography image representing the object based on the first information.

Abstract: A device that may include a narrowband filter that is arranged to pass radiation within a main signal waveband in which a muzzle flash is expected to include energy above a first energy threshold; a first single photon avalanche diode (SPAD) arranged to detect photons of the main signal waveband during different points in time and to output first digital detection signals representative of the photons of the main signal waveband; and a signal processor that is arranged to receive the first digital detection signals and to detect, in response to at least the first digital detection signals, the muzzle flash.

Abstract: The invention comprises a system for determining the state of a charged particle beam, such as beam position, intensity, and/or energy. For example, the charged particle beam state is determined at or about a patient undergoing charged particle cancer therapy using one or more film layers designed to emit photons upon passage of a charged particle beam, which yields information on position and/or intensity of the charged particle beam. The emitted photons are used to calculate position of the treatment beam in imaging and/or during tumor treatment. Optionally and preferably, updating a tomography map uses the same hardware with the same alignment used for cancer therapy at proximately the same time.

Abstract: A method and device, e.g. a C-arm device, for radiographic and nuclear imaging of an object by means of x-ray and gamma emission imaging. The device comprises a support installation with opposed first and second support members, wherein an x-ray source is mounted on the first support member and an x-ray detector on the second support member. The first support member is additionally provided with at least two gamma cameras that are each located adjacent the x-ray source. Each of said at least two gamma cameras comprising a collimator with one or more collimator openings and a gamma radiation detector. Each of the at least two gamma cameras has an associated field of view. The fields of view of the gamma cameras overlap partly, said overlap defining a focus volume that is seen by the at least two gamma cameras. The focus volume is located between the x-ray source and the x-ray detector so that the x-ray beam passes through the focus volume and the focus volume F is seen by the x-ray detector.

Abstract: A scintillator crystal array that is configured to receive rays emitted by an object to be imaged and to emit light energy responsive to the received rays includes plural crystals. At least one of the crystals includes an upper surface, a lower surface disposed opposite the upper surface, plural sides extending between the upper surface and the lower surface, and a micro-crack surface extending at least partially along at least one of the sides. The micro-crack surface includes micro-cracks formed in the crystal configured for controlling distribution of light through the crystal.

Abstract: The present disclosure provides a method comprising: memorizing a sequence of high-resolution images of a scene in a buffer; obtaining radiation emission readings from one or more photo detectors; detecting a suspected flash event based on processing the radiation emission readings from the one or more photo detectors, wherein said detecting occurs at a first instant; retrieving from the buffer high-resolution images of the scene including at least one image that was captured prior to said first instant; and processing the high-resolution images of the scene to determine a geolocation of the suspected flash event.

Abstract: A radiation measurement apparatus includes an array-type radiation detector and an information calculation unit which obtains information on energies detected by pixels of the detector and information on a pixel on which a radiation ray is incident. The information calculation unit includes an energy conversion unit which converts a detected signal of a pixel which is equal to or larger than a predetermined threshold value into a detected energy value, a judgment value calculation unit which obtains a judgment value used to judge whether Compton scattering has been generated in the pixel in accordance with the detected energy, a judgment unit which judges whether the Compton scattering has been generated in the pixel in accordance with the judgment value, and a determination unit which obtains information on a pixel on which a radiation ray is first incident in accordance with a result of the judgment performed by the judgment unit.

Abstract: An apparatus and method of reconstructing a computed tomography (CT) image using multiple datasets of projective measurements, wherein the method of image reconstruction favors spatial correlations among the images respectively reconstructed from each of the corresponding multiple datasets. The multiple data sets each contain projective measurements of the same object taken in close temporal proximity, but taken with different detector type or configurations (e.g., different spectral components in spectral CT or different detector types in hybrid 3rd- and 4th-generation CT scanners). Reconstructed images minimizing a vectorial total variation norm satisfies the criteria of favoring images exhibiting spatial correlations among the reconstructed images and favoring a sparse gradient-magnitude image (i.e., edge enhancing image) for each reconstructed image.

Abstract: A method for extracting photon depth-of-interaction of an incident photon in a crystal with a reflective coating optically coupled to all sides of the crystal, except for an opening, wherein a photodetector is optically coupled to the opening. A pulse shape of a photodetector output as a result of detection of scintillation photons from the crystal generated by the incident photon is measured, wherein the reflective coating optically coupled to all sides of the crystal, except for an opening optically coupled to the photodetector reflects the scintillation photons passing to all sides of the crystal, except for the opening optically coupled to the photodetector. The pulse shape is used to determine photon depth-of-interaction within the crystal.

Abstract: A reconstruction apparatus (9) reconstructs a PET image. A first detector (3) generates first detection events and detection times assigned to the first detection events and a second detector (6) generates second detection events and detection times assigned to the second detection events. A timing window determination unit (11) provides a first-second timing window by providing a first-second upper threshold based on the position of the second detector relative to the first detector and a detection event pairs generation unit (12) generates first-second detection event pairs based on the provided first-second timing window. The first-second detection event pairs are used for reconstructing the PET image. The first-second timing window depends on the position of the second detector leads to an improved generation of first-second detection event pairs, which in turn can lead to an improved PET image.

Abstract: Disclosed herein is a method for removing septal shadows from thick septa collimator images, comprising disposing a line radiation source in a first orientation with respect to an imaging detector; disposing a thick septa collimator between the line radiation source and the imaging detector; where the collimator and the detector move in unison with one another; obtaining a plurality of a line images, where each line image is taken at a different location of the line radiation source with respect to the thick septa collimator; wherein each different location of the line radiation source is along a first linear direction; and relocating the plurality of the line images so obtained to a common location; and summing the images to reduce the septal shadow effects.

Abstract: A radiation imaging apparatus includes a plurality of detection apparatuses configured to output image data based on radiation. The apparatus includes measurement units configured to respectively measure radiation detection levels in the plurality of detection apparatuses; and an irradiation determination unit configured to determine presence/absence of radiation irradiation based on the measured detection levels.

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: A gamma photon detector for detecting 511 keV PET radiation includes a scintillator host material doped with cerium. The cerium is present in a concentration of 0.1 to 1.0 mol %. Lower concentrations increase light output but also decay times which can lead to pile up issues. The higher light output enables the read out area to be decreased which reduces the pile up issues. Embodiments with a cerium concentration as low as 0.15 to 0.2 mol % and a read out area as low as 0.1 cm2 are contemplated.

Abstract: An embodiment of an apparatus for measuring properties of an earth formation includes: a carrier configured to be disposed in a borehole in an earth formation; a scintillation material configured to emit light flashes in response to exposure to radiation, the scintillation material having a surface configured to be directed toward a region of the formation; an array of solid-state photodetectors that extends along at least one surface of the scintillation material, wherein the scintillation material has a shape configured to concentrate the light flashes and direct the light flashes toward the array; and a processor configured to detect signals generated by photo detectors in the array and estimate energy levels and positions of the light flashes within the scintillation material.

Abstract: Methods, devices, systems and computer program products produce and utilize improved momentum estimates for charged particles such as electrons and muons. One method for measuring momentum includes obtaining charged particle tomographic data at one or more charged particle position detectors corresponding to scattering angles of charged particles that pass through an object volume. The distribution of scattering angles associated with the charged particles is determined using measured data collected from the position detectors, based on deviations of local trajectories of the charged particles in one or more planes relative to a reference trajectory. The method also includes determining a length of the scattering material based on the characteristics of the position detectors and the charged particles' angle of incidence on the position detectors, and obtaining charged particle momentum estimates based on the determined distribution of scattering angles and the length of the scattering material.

Abstract: Nuclear medicine (NM) multi-head imaging system includes a plurality of detector units coupled to a gantry. The detector units configured to face toward a center of the bore and including a series of first detector units and a second detector unit. The system also includes at least one processor that, when executing programmed instructions, performs the following operations. The at least one processor rotates the first detector units such that the first detector units face in a common first direction that is generally toward the bore. A working gap exists between the detector FOVs of the respective first detector units. The at least one processor rotates the second detector unit such that the second detector unit faces in a second direction that is opposite the first direction. The detector FOV of the second detector unit covers the working gap.

Abstract: A time to digital converter (TDC) includes a synchronizer configured to receive a stop signal and a master clock signal, wherein the synchronizer is configured to generate a clock stop signal and a counter enable signal. The TDC further includes a coarse counter configured to receive the master clock signal and the counter enable signal, wherein the coarse counter is configured to generate a most significant bits (MSB) signal based on the counter enable signal and the master clock signal. The TDC further includes a delay line counter configured to receive the stop signal and the clock stop signal, wherein the delay line counter is configured to generate a least significant bits (LSB) signal based on the stop signal and the clock stop signal, and the delay line counter is further configured to perform correlated double sampling (CDS).

Abstract: A pixelated gamma detector includes a scintillator column assembly having scintillator crystals and optical transparent elements alternating along a longitudinal axis, a collimator assembly having longitudinal walls separated by collimator septum, the collimator septum spaced apart to form collimator channels, the scintillator column assembly positioned adjacent to the collimator assembly so that the respective ones of the scintillator crystal are positioned adjacent to respective ones of the collimator channels, the respective ones of the optical transparent element are positioned adjacent to respective ones of the collimator septum, and a first photosensor and a second photosensor, the first and the second photosensor each connected to an opposing end of the scintillator column assembly. A system and a method for inspecting and/or detecting defects in an interior of an object are also disclosed.