A terminal capable of detecting rays, an enclosure, and a method for fabricating terminal are provided. The terminal comprises a terminal body and a ray detector in communication with the terminal body. The terminal body comprises a display panel. The ray detector detects rays around the terminal, and transmits the detected signal to the terminal body. The terminal body analyzes the detected signal and transmits the detected signal to the display panel for displaying. In the present disclosure, the detector and the display panel are formed at the same time, and the detector is integrated in a same display panel, so that the process is simplified. The terminal stores and analyzes the data about the collected ionizing radiation dose. As a result, the radiation dose can be read in real time, and an alert can be issued instantaneously to reduce unnecessary damage.

In capturing an image of a grid by an image detector, a measurement pixel that is not in the position of a specific point having a maximum or minimum value of an output signal is referred to as a first measurement pixel, and a measurement pixel that is in the position of the specific point is referred to as a second measurement pixel. The disposition of the first and second measurement pixels are determined so as to satisfy the following condition: fG/fN≠odd number, wherein fG is a grid frequency and fN is a Nyquist frequency of pixels; and in shifting the grid C times by one pixel, the number of the first measurement pixels is larger than that of the second measurement pixels at any time in the range of a cycle C of a repetition pattern appearing in the image.

Provided is a preview image generating section configured to generate preview image during radiography for the purpose of providing a radiation tomography apparatus that allows suppression of unnecessary imaging time by displaying a condition of an image during the radiography in the process of diagnosis. An operator can recognize from the preview image how a subject appears in the image in a radiation tomography apparatus also during the radiography. This allows stopping the radiography before a diagnostic image having a suitable level of clearness for diagnosis is generated. As a result, a shorter imaging time is achieved, and burden to the subject can be suppressed.

A gamma ray generator includes a rotational shaft, a plurality of holders and a plurality of gamma ray sources. The holders are connected to the rotational shaft. The gamma ray sources are disposed in the holders respectively, wherein the holders respectively have an upper portion and a lower portion connecting to the upper portion, and the gamma ray source is placed at an interface between the upper portion and the lower portion.

A gamma ray generator includes a rotational shaft, a plurality of holders and a plurality of gamma ray sources. The holders are connected to the rotational shaft. The gamma ray sources are disposed in the holders respectively, wherein the holders respectively have an upper portion and a lower portion connecting to the upper portion, and the gamma ray source is placed at an interface between the upper portion and the lower portion.

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. A positioning mechanism (35) changes the orientation of the scintillator elements (31), in particular for tilting the scintillator elements (31), to switch between operation modes.

A surgical guidance system offering different levels of imaging capability while maintaining the same hand-held convenient small size of light-weight intra-operative probes. The surgical guidance system includes a second detector, typically an imager, located behind the area of surgical interest to form a coincidence guidance system with the hand-held probe. This approach is focused on the detection of positron emitting biomarkers with gamma rays accompanying positron emissions from the radiolabeled nuclei.

An image detector is disposed behind a grid. The image detector has normal pixels and measurement pixels. Out of a group of measurement pixels based on which an average value of dose measurement signals is calculated, a [C/D] number of measurement pixels are disposed or chosen in a cycle Z=(R×C)±D. Wherein, C represents a cycle of a repetition pattern appearing in an arrangement direction of X-ray transparent layers and X-ray absorbing layers in an X-ray image of the grid, and is represented in units of the number of pixels. R represents a natural number of 0 or more. D represents an integer less than the cycle C. [C/D] represents a maximum integer equal to or less than C/D. Provided that at least the [C/D] number of measurement pixels are shifted C occasions by one pixel, if D=1, the average value of the dose measurement signals is invariable without any variations.

Provided herein is a phantom and a phantom system, the phantom including a plurality of blocks combined having different elastic modulus, and thus may be easily manufactured in various shapes, movements, and densities and may exactly imitate movements of a tissue such as in a lung that has high volume change rates and has a high possibility that a position and shape of a tumor may change, thereby providing an effect of being used in replacement of patients when evaluating 4D-CT performance and measuring radiation amounts.

Radiation detectors are disclosed. The radiation detectors comprise a substrate and at least one radiation sensitive region on the substrate, the at least one radiation sensitive region comprising an array of elongate nanostructures projecting from the substrate. Methods of manufacture of such radiation detectors are also disclosed.