A time-of-flight positron emission tomography (TOFPET) assembly for detecting lesions of a breast of a subject, wherein the subject may anatomically be defined with a median plane and chest wall-coronal plane. The assembly may comprise: a detector array having at least two or more detector segments. The detector segments may include: a scintillator for placement toward the target, the scintillator having a top edge generally closest to the subject and a detection surface wall aligned closest to surrounding the breast, a photo multiplier opposite the scintillator, and a readout connected to the photo multiplier. The assembly may also comprise a processor that receives the acquired tracer emission signals and converts the signals into a three dimensional, tomographic image reconstruction. The detector array is defined by a ring surrounding the breast and the face of ring that may be tilted to offset the chest wall-coronal plane of the subject, and wherein one of the top edges of one of the detector segments is above the chest wall-coronal plane of the subject in the posterior direction.

A time-of-flight positron emission tomography (TOFPET) assembly for detecting lesions of a breast of a subject, wherein the subject may anatomically be defined with a median plane and chest wall-coronal plane. The assembly may comprise: a detector array having at least two or more detector segments. The detector segments may include: a scintillator for placement toward the target, the scintillator having a top edge generally closest to the subject and a detection surface wall aligned closest to surrounding the breast, a photo multiplier opposite the scintillator, and a readout connected to the photo multiplier. The assembly may also comprise a processor that receives the acquired tracer emission signals and converts the signals into a three dimensional, tomographic image reconstruction. The detector array is defined by a ring surrounding the breast and the face of ring that may be tilted to offset the chest wall-coronal plane of the subject, and wherein one of the top edges of one of the detector segments is above the chest wall-coronal plane of the subject in the posterior direction.

A digital radiographic detector outputs positive read out signals that may oscillate. The presence of negative going portions of the read out signals may be used to determine that the detected positive signals are a result of noise, while an absence of the negative going portions may be used to determine that x-rays are impacting the detector.

A method for geometric calibration of a radiography apparatus acquires tomosynthesis projection images of patient anatomy from a detector and an x-ray source translated along a scan path. An epipolar geometry is calculated according to the relative position of the detector to the scan path by estimating a direction for epipolar lines that extend along an image plane that includes the detector. A region of interest of the patient anatomy that is a portion of each projection image and is fully included within each projection image in the series is defined. A consistency metric is calculated for estimated epipolar lines extending within the ROI. The method iteratively adjusts the epipolar line estimation until the consistency metric indicates accuracy to within a predetermined threshold. A portion of a tomosynthesis volume is reconstructed and displayed.

A method and apparatus for testing the response of protective headgear 104 to impact forces. A high-speed cineradiography imaging system 100 is used to obtain full-field, time-resolved internal monitoring and measurement of headgear component (pads 140 and liners 142) deformation and interaction with a head surrogate (headform 102), deformation of headform components, and stress and strain transfer into the headform. Radiopaque contrast materials (144 & 148) and integration techniques are used to highlight specific regions of interest within the headgear and headform components during the impact loading events.

The present disclosure relates to systems and methods for image data processing. A first correction coefficient corresponding to a first collimation width of a collimator of a scanner may be obtained. The collimator may have a collimation width being adjustable. A relationship between scattered radiation intensities and collimation widths may be obtained. A relationship between correction coefficients and collimation widths may be determined based on the first correction coefficient, the first collimation width, and the relationship between scattered radiation intensities and collimation widths. A target collimation width of the collimator may be obtained. A target correction coefficient may be determined based on the target collimation width and the relationship between correction coefficients and collimation widths.

The present technology relates to a radiation detection apparatus that makes it possible to obtain a projection image of a radiation in a short period of time. The radiation detection apparatus includes a scintillator that emits scintillation light in response to incidence of a radiation, a pixel substrate on which a plurality of pixels each of which photoelectrically converts the scintillation light and outputs a pixel signal according to a light amount of the scintillation light is disposed in an array, a detection circuit substrate that includes an A/D (Analog to Digital) conversion unit for A/D converting the pixel signal and is stacked on the pixel substrate, and a compression unit that compresses digital data outputted from the A/D conversion unit. The present technology can be applied, for example, to an X-ray imaging apparatus that detects an X-ray to perform imaging and so forth.

The present technology relates to a radiation detection apparatus that makes it possible to obtain a projection image of a radiation in a short period of time. The radiation detection apparatus includes a scintillator that emits scintillation light in response to incidence of a radiation, a pixel substrate on which a plurality of pixels each of which photoelectrically converts the scintillation light and outputs a pixel signal according to a light amount of the scintillation light is disposed in an array, a detection circuit substrate that includes an A/D (Analog to Digital) conversion unit for A/D converting the pixel signal and is stacked on the pixel substrate, and a compression unit that compresses digital data outputted from the A/D conversion unit. The present technology can be applied, for example, to an X-ray imaging apparatus that detects an X-ray to perform imaging and so forth.

The disclosure relates to PET imaging systems and methods. The systems may execute the methods to obtain an anatomical image of a subject acquired when the subject remains in a breath-hold status; obtain PET data of the subject, the PET data corresponding to a respiration signal with a plurality of respiratory phases of the subject, the respiratory phases including a first respiratory phase and a second respiratory phase; gate the PET data; reconstruct a plurality of gated PET images, the plurality of gated PET images including a first gated PET image corresponding to the first respiratory phase and a second gated PET image corresponding to the second respiratory phase; determine a first motion vector field between the first gated PET image and the second gated PET image; determine a second motion vector field between the anatomical image and the second gated PET image; and reconstruct an attenuation corrected PET image.

A method for imaging an object to be reconstructed includes acquiring projection data corresponding to the object. Furthermore, the method includes generating a measured sinogram based on the acquired projection data and formulating a forward model, where the forward model is representative of a characteristic of the imaging system. In addition, the method includes generating an estimated sinogram based on an estimated image of the object and the forward model and formulating a statistical model based on at least one of pile-up characteristics and dead time characteristics of a detector of the imaging system. Moreover, the method includes determining an update corresponding to the estimated image based on the statistical model, the measured sinogram, and the estimated sinogram and updating the estimated image based on the determined update to generate an updated image of the object. Additionally, the method includes outputting a final image of the object.