A first image data set and at least one second image data set are captured, and a contrast-enhanced image data set and a non-contrast image data set are determined based on the first and the at least one second image data set. The perfusion image data set is calculated based on a ratio of image values of the contrast-enhanced image data set and locally corresponding image values of the non-contrast image data set, and the perfusion image data set is provided via a second interface.

An apparatus, system and method for calibrating an x-ray apparatus including acquiring sinogram data by scanning a symmetrical phantom using a plurality of detector channels; generating mirror-copied sinogram data by mirror-copying at least one of first sinogram data and second sinogram data of the acquired sinogram data, wherein the first sinogram data and the second sinogram data are generated by dividing the sinogram data at a center detector channel of the plurality of detector channels; outputting a first reconstructed image by reconstructing the mirror-copied sinogram data; and determining a calibration parameter based on the first reconstructed image.

An extra-oral dental imaging apparatus for obtaining an image from a patient has a radiation source; a first digital imaging sensor that provides, for each of a plurality of image pixels, at least a first digital value according to a count of received photons that exceed at least a first energy threshold; a mount that supports the radiation source and the first digital imaging sensor on opposite sides of the patient's head; a computer in signal communication with the digital imaging sensor for acquiring a first two-dimensional image from the first digital imaging sensor; and a second digital imaging sensor that is alternately switched into place by the mount and that provides image data according to received radiation.

A PET/CT imaging system is provided. The imaging system includes a PET detection system having a plurality of detector rings and an axial gap between at least two adjacent detector rings within the plurality of detector rings. The imaging system includes a CT system having an x-ray generator and a CT detection system positioned within the axial gap between the at least two detector rings. The system is configured to collect PET data and CT data on the same volume of interest substantially simultaneously.

The invention relates to a detection apparatus (12) for detecting photons. The detection apparatus comprises a pile-up determining unit (15) for determining whether detection signal pulses being indicative of detected photons are caused by a pile-up event or by a non-pile-up event, wherein a detection values generating unit (16) generates detection values depending on the detection signal pulses and depending on the determination whether the respective detection signal pulse is caused by a pile-up event or by a non-pile-up event. In particular, the detection values generating unit can be adapted to reject the detection signal pulses caused by pile-up events while generating the detection values. This allows for an improved quality of the generated detection values.

An imaging system is provided that includes a gantry having a bore extending therethrough; a plurality of image detectors attached to the gantry and radially spaced around a circumference of the bore such that gaps exist between image detectors along the circumference of the bore; an x-ray source attached to the gantry, wherein the x-ray source transmits x-rays across the bore towards at least two of the image detectors; wherein at least two image detectors detect both emission radiation and x-ray radiation.

A method and apparatus for estimating a parameter vector including a plurality of parameters of a detector response model of a photon-counting detector. The method includes calculating a modeled spectrum based on an input spectrum and an initial value of the plurality of parameters. For each detector, a difference between the normalized photon count of the measured spectrum and the normalized modeled spectrum is calculated. A root mean square error (RMSE) between the measured and modeled spectra is obtained by squaring the normalized difference and weighting the normalized difference by a weighting factor. The parameter vector is updated until an optimum RMSE value is achieved. Upon determining optimal values of the parameter vector, measured data that is obtained via a patient scan is corrected based on the optimal parameter vector.

Single X-ray grating differential phase contrast (DPC) X-ray imaging is provided by replacing the conventional X-ray source with a photo-emitter X-ray source array (PeXSA), and by replacing the conventional X-ray detector with a photonic-channeled X-ray detector array (PcXDA). These substitutions allow for the elimination of the G0 and G2 amplitude X-ray gratings used in conventional DPC X-ray imaging. Equivalent spatial patterns are formed optically in the PeXSA and the PcXDA. The result is DPC imaging that only has a single X-ray grating (i.e., the G1 X-ray phase grating).

There is provided an x-ray detector system including a photon-counting x-ray detector for detecting x-ray radiation from an x-ray source, and a coincidence detection system configured to determine and/or obtain information about the radiation incident on the x-ray detector based on information about the time of photon interactions in the x-ray detector and information about the location of the x-ray source in relation to the x-ray detector. There is also provide an x-ray imaging system including such an x-ray detector system, as well as a corresponding coincidence detection system and a corresponding method.

According to embodiment, an X-ray computed tomography apparatus includes an X-ray tube, an X-ray detector including a scintillator generating scintillation light upon incidence of X-ray photons and a photodetection element, a peak value detector detecting peak values corresponding to X-ray photons based on an output signal from the element, processing circuitry determining an attenuation characteristic of the light by each X-ray photon and an output decreased characteristic of the element, based on the values and time when each peak value was detected, correcting the detected values according to the characteristics, a counter counting the X-ray photons corresponding to the respective corrected peak values, wherein the processing circuitry reconstructs a medical image based on an output from the counter.