The present disclosure provides systems and methods for performing quality control assessments of a three dimensional (3D) printing system. In particular, the present disclosure provides a phantom designs for use in 3D printing systems, as well as methods of quality control for a 3D printing system performed using a 3D printed phantom.

An X-ray phase contrast imaging system includes an X-ray source, a detector, a plurality of gratings including a first grating and a second grating, and a grating positional displacement acquisition section configured to obtain a positional displacement of the grating based on a Fourier transform image obtained by Fourier transforming an interference fringe image detected by the detector.

A method for determining the position and/or orientation of at least one sensor system relative to the base structure of a scanning system during scanning of an object, the method includes obtaining one or more tracking images using one or more cameras, where the cameras are in a fixed position with respect to the sensor system; and determining from the one or more tracking images the position and/or orientation of the sensor system relative to the base structure at a given time.

3D image data of a skeletal portion is acquired. A location of a proximal portion of a tool is calculated and a location is derived of a distal portion of the tool with respect to the skeletal portion, with respect to the 3D image data. A display indicates the derived location. First and second 2D images of the distal portion of the tool are acquired from two different poses of a 2D imaging device with respect to the subject and registered with the 3D image data. The location of the distal portion with respect to the 3D image data of the skeletal portion is determined based on the registration and an identified location of the distal portion within the 2D x-rays. Based upon the determined location, the display updates the indicated location of the distal portion. Other embodiments are also described.

A computed tomography (CT) system includes a rotatable gantry having an opening to receive an object to be scanned, an x-ray tube, a pixelated detector positioned on the rotatable gantry to receive the x-rays from the x-ray tube, and a computer programmed to acquire helical CT data, determine a sunrise (SR) view position for each pixel within a SR index image, and determine a sunset (SS) view position for each pixel within a SS index image, for a given reference image slice, wherein the SR view position is a first angle of an illumination range for a voxel and the SS view position is a last angle of the illumination range for the voxel, for all slices, rotate the SR index image and the SS index image through a projection index, and reconstruct an image based on the rotated SR index image and the SS index image.

The disclosure relates to a system and method for calibrating a medical system. The method may include one or more of the following operations. Projection data of a phantom comprising a plurality of markers may be acquired from an imaging device, at a plurality of angles of a source of the imaging device. A plurality of projection matrices of a first coordinate system relating to the phantom and a transformation matrix between the first coordinate system and a second coordinate system relating to the imaging device may be determined based on the projection data of the phantom and coordinates of the plurality of markers in the first coordinate system. A plurality of projection matrices of the second coordinate system may be determined based on the plurality of projection matrices of the first coordinate system and the transformation matrix.

An imaging method (100) includes: acquiring first training images of one or more imaging subjects using a first image acquisition device (12); acquiring second training images of the same one or more imaging subjects as the first training images using a second image acquisition device (14) of the same imaging modality as the first imaging device; and training a neural network (NN) (16) to transform the first training images into transformed first training images having a minimized value of a difference metric comparing the transformed first training images and the second training images.

Disclosed are a backscattered ray shielding mechanism and a portable X-ray generating device comprising the same. The backscattered ray shielding mechanism according to the present invention is mounted on a portable X-ray generating hand-held device to emit X-rays and blocking backscattered X-rays during X-ray emission and includes a lead-free lightweight shielding member, which is detachably or foldably mounted as a convertible form on an X-ray emitting unit of the portable X-ray generating device and partially supported by the X-ray emitting unit.

Disclosed is a calibration phantom for an x-ray imaging system having an x-ray source and an x-ray detector. The calibration phantom includes a combination of geometric objects of at least three different types and/or compositions including: a first object located in the middle, including a first material; a plurality of second objects arranged around the periphery of the first object, at least a subset of the second objects including a second material different than the first material, wherein the first object is relatively larger than the second objects; a plurality of third objects arranged around the periphery of the first object and/or around the periphery of at least a subset of the second objects, at least a subset of the third objects including a third material different than the first material and the second material, wherein the third objects are relatively smaller than the second objects.

A method for geometric calibration of a radiography apparatus disposes at least one radio-opaque marker in the field of view of the radiography apparatus. A series of tomosynthesis projection images of patient anatomy is acquired from the detector with the x-ray source at different positions along a scan path. For at least three projection images showing the position of the radio-opaque marker, the spatial and angular geometry of the x-ray source and detector are calculated according to the positions of the marker. A tomosynthesis image is reconstructed according to the calculated geometry. A rendering of the reconstructed image is displayed.