Abstract: An apparatus for beta-emission two-dimensional imaging including: a beta ray detector configured to receive, from an imaging target containing a first nuclide and a second nuclide, a beta ray based on the first or second nuclide and thereby detect the beta ray, the beta ray detector outputting a beta ray detection signal including location information indicating a detection location of the beta ray on a two-dimensional basis; a gamma ray detector configured to detect a gamma ray, the gamma ray detector detecting the first and second peculiar gamma rays in a discriminable manner; and an imaging processor configured to be capable of generating a distribution image of the first nuclide and a distribution image of the second nuclide in a discriminable manner.

Abstract: A PET system with a positron lifetime measurement function includes: a first gamma ray detector configured to receive, from an imaging target containing a nuclide that goes into an excited state of a daughter nucleus by undergoing beta decay and that then, subsequently to emission of a positron resulting from the beta decay, emits a deexcitation gamma ray when transiting into a ground state of the daughter nucleus, three annihilation gamma rays resulting from the positron annihilating with an electron, the first gamma ray detector thereby detecting the three annihilation gamma rays; a second gamma ray detector configured to detect the deexcitation gamma ray; and a processor configured to derive, in three dimensions, a distribution state of the nuclide in the imaging target and to determine information on a positron lifetime in association with a derived distribution position.

Abstract: A PET system with a positron lifetime measurement function includes: a first gamma ray detector configured to receive, from an imaging target containing a nuclide that goes into an excited state of a daughter nucleus by undergoing beta decay and that then, subsequently to emission of a positron resulting from the beta decay, emits a deexcitation gamma ray when transiting into a ground state of the daughter nucleus, three annihilation gamma rays resulting from the positron annihilating with an electron, the first gamma ray detector thereby detecting the three annihilation gamma rays; a second gamma ray detector configured to detect the deexcitation gamma ray; and a processor configured to derive, in three dimensions, a distribution state of the nuclide in the imaging target and to determine information on a positron lifetime in association with a derived distribution position.

Abstract: An apparatus for beta-emission two-dimensional imaging including: a beta ray detector configured to receive, from an imaging target containing a first nuclide and a second nuclide, a beta ray based on the first or second nuclide and thereby detect the beta ray, the beta ray detector outputting a beta ray detection signal including location information indicating a detection location of the beta ray on a two-dimensional basis; a gamma ray detector configured to detect a gamma ray, the gamma ray detector detecting the first and second peculiar gamma rays in a discriminable manner; and an imaging processor configured to be capable of generating a distribution image of the first nuclide and a distribution image of the second nuclide in a discriminable manner.

Abstract: To make correct determination of electric charge collection among signals from a semiconductor radiation detector, provided in an embodiment of the present invention is a signal data processing method. The method includes a step of calculating timing data sequences unique to channels (timing data calculation step S02), each of channels corresponding to each of plural electrodes of the radiation detector, from detection signal data sequences. Then, while making a comparison with a first threshold value, a data value for the timing data sequence at timing when a predetermined delay time is elapsed after the timing data sequence reached the first predetermined value is selected as a timing data value for determination for the channel (delay and selection step S04).

Abstract: A skin cleansing agent composition of the present invention contains an isotropic liquid phase, which is a bicontinuous structure, and containing: 15 to 30 mass % of a nonionic surfactant having HLB of higher than 9 and equal to or lower than 20; 1 to 15 mass % of a nonionic surfactant having HLB of equal to or higher than 5 and equal to or lower than 9; 10 to 40 mass % of an oil agent exhibiting a viscosity at 30 degrees C. of equal to or lower than 30 mPa·s; 10 to 40 mass % of a water-soluble solvent having 3 or more of hydroxyl groups in single molecule; 10 to 30 mass % of a water-soluble solvent having 1 or 2 hydroxyl group(s) in single molecule; 0.05 to 1.0 mass % of a water-soluble polymer containing (meta)acrylic acid as a configuration unit and/or an acryloyl methyl taurate-vinylpyrrolidone copolymer; 0.001 to 2.0 mass % of a water-soluble inorganic salt and/or an organic salt having 1 to 8 carbon atoms; and water.

Abstract: In the present invention, to conduct multiple molecular imaging in a PET device, both a first probe and a second probe, each of which has a nuclide that emits unique gamma rays as a result of gamma decay after beta decay, are administered to a subject to be imaged, and then the image capturing is performed by a multiple probe PET device (100). The multiple probe PET device (100) is provided with a group of PET gamma ray detectors (10) and an energy-resolving gamma ray detector (20), and, when an imaging processor (30) executes image reconstruction based on a pair-annihilation detection signal from the group of PET gamma ray detectors (10), images are reconstructed differently according to the energy values of the unique gamma rays. Imaging can also be carried out using a nuclide that does not emit any unique gamma ray and a nuclide that emits a unique gamma ray.

Abstract: To make correct determination of electric charge collection among signals from a semiconductor radiation detector, provided in an embodiment of the present invention is a signal data processing method. The method includes a step of calculating timing data sequences unique to channels (timing data calculation step S02), each of channels corresponding to each of plural electrodes of the radiation detector, from detection signal data sequences. Then, while making a comparison with a first threshold value, a data value for the timing data sequence at timing when a predetermined delay time is elapsed after the timing data sequence reached the first predetermined value is selected as a timing data value for determination for the channel (delay and selection step S04).

Abstract: To simultaneously image a plurality types of tracer molecules for a Compton image and a PET image. Provided is an imaging device comprising: a first Compton camera (10) for receiving one gamma ray emitted from an imaging target (900) administered by first probe having positron emitting nuclei and second probe having gamma ray emission nuclei; and a second Compton camera (20) which is arranged opposite to the first Compton camera (10) and receives another gamma ray emitted from the imaging target (900). The imaging device is also provided with: an imaging processor for distinguishing and reconstructing a PET image and a Compton image in accordance with the combination of the Compton cameras which detected the gamma rays; and a display for displaying the PET image and the Compton image in association respectively with the first and the second probes.

Abstract: In the present invention, to conduct multiple molecular imaging in a PET device, both a first probe and a second probe, each of which has a nuclide that emits unique gamma rays as a result of gamma decay after beta decay, are administered to a subject to be imaged, and then the image capturing is performed by a multiple probe PET device (100). The multiple probe PET device (100) is provided with a group of PET gamma ray detectors (10) and an energy-resolving gamma ray detector (20), and, when an imaging processor (30) executes image reconstruction based on a pair-annihilation detection signal from the group of PET gamma ray detectors (10), images are reconstructed differently according to the energy values of the unique gamma rays. Imaging can also be carried out using a nuclide that does not emit any unique gamma ray and a nuclide that emits a unique gamma ray.

Abstract: A skin cleansing agent composition of the present invention contains an isotropic liquid phase, which is a bicontinuous structure, and containing: 15 to 30 mass % of a nonionic surfactant having HLB of higher than 9 and equal to or lower than 20; 1 to 15 mass % of a nonionic surfactant having HLB of equal to or higher than 5 and equal to or lower than 9; 10 to 40 mass % of an oil agent exhibiting a viscosity at 30 degrees C. of equal to or lower than 30 mPa·s; 10 to 40 mass % of a water-soluble solvent having 3 or more of hydroxyl groups in single molecule; 10 to 30 mass % of a water-soluble solvent having 1 or 2 hydroxyl group(s) in single molecule; 0.05 to 1.0 mass % of a water-soluble polymer containing (meta)acrylic acid as a configuration unit and/or an acryloyl methyl taurate-vinylpyrrolidone copolymer; 0.001 to 2.0 mass % of a water-soluble inorganic salt and/or an organic salt having 1 to 8 carbon atoms; and water.

Abstract: To simultaneously image a plurality types of tracer molecules for a Compton image and a PET image. Provided is an imaging device comprising: a first Compton camera (10) for receiving one gamma ray emitted from an imaging target (900) administered by first probe having positron emitting nuclei and second probe having gamma ray emission nuclei; and a second Compton camera (20) which is arranged opposite to the first Compton camera (10) and receives another gamma ray emitted from the imaging target (900). The imaging device is also provided with: an imaging processor for distinguishing and reconstructing a PET image and a Compton image in accordance with the combination of the Compton cameras which detected the gamma rays; and a display for displaying the PET image and the Compton image in association respectively with the first and the second probes.

Abstract: The apparatus has an energy calculation section 32 that calculates energy deposit values of interactions based on signals obtained from segmented electrodes 11, 12 provided on two opposite surfaces of a semiconductor crystal, a reference waveform storing section 33 that stores beforehand waveforms that will be obtained from the segmented electrodes when a single interaction occurs for multiple positions in the crystal, a waveform synthesis section 34 that synthesizes reference waveforms corresponding to arbitrary two points in the crystal as candidate points of interaction at a ratio equal to a ratio of their energy deposit values, and a comparison section 35 that compares a measured waveform and the synthesized waveforms. The candidate points from which the synthesized waveform most similar to the measured waveform is obtained is determined to be the positions of interactions. Thus, even in cases where multiple interactions occur, the positions of the interactions can be detected.

Abstract: The apparatus has an energy calculation section 32 that calculates energy deposit values of interactions based on signals obtained from segmented electrodes 11, 12 provided on two opposite surfaces of a semiconductor crystal, a reference waveform storing section 33 that stores beforehand waveforms that will be obtained from the segmented electrodes when a single interaction occurs for multiple positions in the crystal, a waveform synthesis section 34 that synthesizes reference waveforms corresponding to arbitrary two points in the crystal as candidate points of interaction at a ratio equal to a ratio of their energy deposit values, and a comparison section 35 that compares a measured waveform and the synthesized waveforms. The candidate points from which the synthesized waveform most similar to the measured waveform is obtained is determined to be the positions of interactions. Thus, even in cases where multiple interactions occur, the positions of the interactions can be detected.