An apparatus for detecting a locating medium in tissue includes a probe, and a console. The probe includes a handle and a detector disposed on a distal end of the probe. The console is in communication and includes a display. The display has a first graphical representation and a second graphical representation. The first graphical representation is configured to depict a count real-time count based on a signal from the detector. The second graphical representation is configured to depict a target count.

An apparatus for detecting a locating medium in tissue includes a probe, and a console. The probe includes a handle and a detector disposed on a distal end of the probe. The console is in communication and includes a display. The display has a first graphical representation and a second graphical representation. The first graphical representation is configured to depict a count real-time count based on a signal from the detector. The second graphical representation is configured to depict a target count.

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.

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.

An electronic cassette is provided with a sensor panel, a housing, operation buttons, a head-bottom setting section, lamps and a memory. The sensor panel has a quadrangle imaging area, and detects an X-ray image of a patient. The housing houses the sensor panel. The operation buttons are disposed on the housing. When either one of the operation buttons is pushed down, the head-bottom setting section sets either one of adjoining two sides of the imaging area to be the head of the radiographic image in the display orientation. The display section is disposed on the housing, and displays which side is set by the head-bottom setting section to be the head of the radiographic image. The memory stores head-bottom setting information and the radiographic image in association with each other.

An electronic cassette is provided with a sensor panel, a housing, operation buttons, a head-bottom setting section, lamps and a memory. The sensor panel has a quadrangle imaging area, and detects an X-ray image of a patient. The housing houses the sensor panel. The operation buttons are disposed on the housing. When either one of the operation buttons is pushed down, the head-bottom setting section sets either one of adjoining two sides of the imaging area to be the head of the radiographic image in the display orientation. The display section is disposed on the housing, and displays which side is set by the head-bottom setting section to be the head of the radiographic image. The memory stores head-bottom setting information and the radiographic image in association with each other.

A novel technique of quantifying nuclear medicine data is provided. The novel technique is characterized in that information acquired from nuclear medicine image data is normalized with bone mineral content (BMC) or bone mineral density (BMD). Some embodiments use, instead of the conventional SUV, the SUVbone that has been invented by the inventors of the present application such as the following: SUVbone={Amount of attenuation-corrected radioactivity in region of interest (kBq)÷Volume of region of interest (ml)}/{Administered radioactivity dose (kBq)÷Bone mineral content (g)} or SUVbone={Amount of attenuation-corrected radioactivity in region of interest (kBq)÷Volume of region of interest (ml)}/{Administered radioactivity dose (kBq)÷Bone mineral density (g/m.sup.2)}. BMC or BMD may be estimated from sex, age, height, or weight of a subject.

A novel technique of quantifying nuclear medicine data is provided. The novel technique is characterized in that information acquired from nuclear medicine image data is normalized with bone mineral content (BMC) or bone mineral density (BMD). Some embodiments use, instead of the conventional SUV, the SUVbone that has been invented by the inventors of the present application such as the following: SUVbone={Amount of attenuation-corrected radioactivity in region of interest (kBq)÷Volume of region of interest (ml)}/{Administered radioactivity dose (kBq)÷Bone mineral content (g)} or SUVbone={Amount of attenuation-corrected radioactivity in region of interest (kBq)÷Volume of region of interest (ml)}/{Administered radioactivity dose (kBq)÷Bone mineral density (g/m.sup.2)}. BMC or BMD may be estimated from sex, age, height, or weight of a subject.

A flat pixel (20) is a single unit composing a radiation detector and is configured so as to be divided into at least four subpixels (21) such that even if a prescribed number of subpixels (21) are removed from each pixel (20) in order of largest effective area, the centroid (51) of the effective area of the entirety of the remaining subpixels (21) is positioned within a similar-shape region (30) having the same centroid (50) as the pixel (20) and having sides of lengths that are half those of the pixel (20).

A flat pixel (20) is a single unit composing a radiation detector and is configured so as to be divided into at least four subpixels (21) such that even if a prescribed number of subpixels (21) are removed from each pixel (20) in order of largest effective area, the centroid (51) of the effective area of the entirety of the remaining subpixels (21) is positioned within a similar-shape region (30) having the same centroid (50) as the pixel (20) and having sides of lengths that are half those of the pixel (20).