A nuclear medicine diagnosis apparatus according to an embodiment includes a scintillator configured to emit self-radiation, storage, and processing circuitry. The storage stores first detection efficiency correction data that is generated based on an external radiation source or a simulation and first detection efficiency data per scintillator that is calculated based on radiation that is emitted from the scintillator. The processing circuitry calculates second detection efficiency data per scintillator that is calculated based on radiation that is emitted from the scintillator and generates second detection efficiency correction data based on the first detection efficiency correction data, the first detection efficiency data, and the second detection efficiency data.

Disclosed herein is a method comprising: obtaining a third image from a first X-ray detector when the first X-ray detector and a second X-ray detector are misaligned; determining, based on a shift between a first image and the third image, a misalignment between the first X-ray detector and the second X-ray detector when the first and second detectors are misaligned; wherein the first image is an image the first X-ray detector should capture if the first and the second detectors are aligned.

According to one embodiment, a photon-counting detector (PCD) includes a plurality of macro-pixels. The plurality of macro-pixels arranged on a semiconductor crystal has a first face and a second face. The first face and the second face are parallel. Each macro-pixel from the plurality of macro-pixels is configured to acquire projection data for generating a reconstructed image. The plurality of macro-pixels each includes at least one large micro-pixel is disposed within the each macro-pixel and at least two small micro-pixels is disposed within the each macro-pixel. Each of the at least two small micro-pixels has a surface area that is less than a surface area of the at least one large micro-pixel.

The techniques disclosed may be used to detect and correct channel gain errors resulting from X-ray focal spot mis-alignment during the course of a scan. One benefit of the present invention relative to conventional techniques is that additional hardware is not required for detection of focal spot drift. Instead, the static mis-alignment of each blade is taken into account as part of estimating and correcting X-ray focal spot drift or mis-alignment. In this manner, the risk of image artefacts due to focal spot motion is reduced and the need for costly hardware solutions to detect focal spot motion is avoided.

Systems, devices, and methods are presented for automatic tuning, calibration, and verification of radiation therapy systems comprising control elements configured to control parameters of the radiation therapy systems based on images obtained using electronic portal imaging devices (EPIDs) included in the radiation therapy system.

The invention relates to off-center detector 3D X-ray or proton radiography reconstruction. Redundancy weighting with a steep weighting function around the iso-axis typically leads to artifacts in the reconstruction, for example, if inconsistencies between two nominal redundant projections occur, e.g. due to slightly incorrect detector calibration or scatter correction, etc. With the present invention, an approach is presented for overcoming or mitigating these problems.

Systems, devices, and methods are presented for automatic tuning, calibration, and verification of radiation therapy systems comprising control elements configured to control parameters of the radiation therapy systems based on images obtained using electronic portal imaging devices (EPIDs) included in the radiation therapy system.

Timing calibration of a positron emission tomography (PET) imaging device (2) uses a radioactive source (20) comprising a positron-emitting radioisotope having a decay path including emission of two oppositely directed 511 keV gamma rays and a cascade gamma ray at a cascade gamma ray energy. A timestamped radiation detection event data set acquired from the radioactive source by the PET imaging device is processed using energy window filtering (32) and time window filtering (36) to generate a coincidence data set (40, 42, 44) including event pairs (40) each consisting of two coincident 511 keV events and cascade event pairs (42) or triplets (44) each consisting of at least one coincident 511 keV event and a coincident cascade event at the cascade gamma ray energy. A timing calibration (12) is generated using the coincidence data set. The timing calibration comprises offset times for PET detectors of the PET imaging device.

An X-ray CT apparatus according to one embodiment includes a photon counting detector and a processing circuitry. The photon counting detector includes a plurality of detecting elements configured to detect X-rays. The processing circuitry is configured to set a control parameter corresponding to a position of each detecting element of the plurality of detecting elements in the photon counting detector.

Some embodiments include a system, comprising: an integrating detector including a plurality of pixels, each pixel configured to integrate signal from photons of a radiation beam; and an energy sensing detector overlapping the plurality of pixels of the integrating detector and configured to generate energy information in response to the radiation beam.