Abstract: A bone density measuring apparatus and a bone density imaging method capable of improving the accuracy of a bone density analysis are provided. In a state in which no subject is present, a detector detects X-rays emitted from an X-ray tube under a high tube voltage X-ray condition/a low tube voltage X-ray condition and a first gain correction map/a second gain correction map is generated (S1, S2). A detector detects the X-rays emitted from an X-ray tube and transmitted through a subject under a high tube voltage X-ray condition/a low tube voltage X-ray condition, and a high voltage image/a low voltage image captured by the detector is generated (S3).

Abstract: A safety cabinet has a second operation chamber in a first operation chamber and into which clean air is supplied, a second suction opening for sucking in air in the second operation chamber and a portion of the air in the first operation chamber, and a second operation opening part that is provided facing a first operation opening part and communicates the second operation chamber with the first operation chamber. Airflow containment (air barrier) is doubled with respect to the outside of a safety cabinet. In cases where decontamination and disinfection operations are carried out according to the changeover procedures, intensive decontamination and disinfection of the second operation chamber is sufficient, and decontamination and disinfection of the first operation chamber is hardly required. Decontamination and disinfection operations in the changeover procedures and the like can be carried out in a greatly reduced time.

Abstract: An X-ray fluoroscopic device includes an X-ray imaging mechanism having an X-ray tube 1 and a flat panel detector 2; filters 23 to form a correction region, in which the scattered radiation S caused by irradiating the therapeutic beam to the subject 57 can be incident, but the X-ray that is irradiated from the X-ray tube 1 and transmits through the subject 57 cannot be incident; and a correction element that corrects the data of the region other than the correction region of the flat panel detector 2 by using the data of the correction region of the flat panel detector 2.

Abstract: A safety cabinet has a second operation chamber in a first operation chamber and into which clean air is supplied, a second suction opening for sucking in air in the second operation chamber and a portion of the air in the first operation chamber, and a second operation opening part that is provided facing a first operation opening part and communicates the second operation chamber with the first operation chamber. Airflow containment (air barrier) is doubled with respect to the outside of a safety cabinet. In cases where decontamination and disinfection operations are carried out according to the changeover procedures, intensive decontamination and disinfection of the second operation chamber is sufficient, and decontamination and disinfection of the first operation chamber is hardly required. Decontamination and disinfection operations in the changeover procedures and the like can be carried out in a greatly reduced time.

Abstract: An X-ray fluoroscopic device includes an X-ray imaging mechanism having an X-ray tube 1 and a flat panel detector 2; filters 23 to form a correction region, in which the scattered radiation S caused by irradiating the therapeutic beam to the subject 57 can be incident, but the X-ray that is irradiated from the X-ray tube 1 and transmits through the subject 57 cannot be incident; and a correction element that corrects the data of the region other than the correction region of the flat panel detector 2 by using the data of the correction region of the flat panel detector 2.

Abstract: An optical product according to the present invention includes a transparent base material, and a multilayer film including a dielectric film and an ITO film. The multilayer film is formed on one face or two faces of the transparent base material. The physical thickness of the ITO film is not less than 3 nanometers and not greater than 7 nanometers. The ITO film can be formed by vapor deposition with plasma treatment.

Abstract: An optical product according to the present invention includes a transparent base material, and a multilayer film including a dielectric film and an ITO film. The multilayer film is formed on one face or two faces of the transparent base material. The physical thickness of the ITO film is not less than 3 nanometers and not greater than 7 nanometers. The ITO film can be formed by vapor deposition with plasma treatment.

Abstract: An X-ray tube and a flat panel X-ray detector (FPD) are constructed movable parallel to each other in the same direction along a body axis which is a longitudinal direction of a patient. The X-ray tube intermittently emits radiation and the FPD detects radiation transmitted through the patient irradiated intermittently whenever the X-ray tube and FPD move every pitch. X-ray images O1, O2, . . . , OI, . . . , and OM are decomposed for every pitch noted above. The decomposed images are composed for each projection angle to obtain projection images P1, P2 and so on. Therefore, a sectional image with a long field of view in the longitudinal direction can be obtained by carrying out a reconstruction process based on the composed projection images.

Abstract: An X-ray tube and a flat panel X-ray detector (FPD) are constructed movable parallel to each other in the same direction along a body axis which is a longitudinal direction of a patient. The X-ray tube intermittently emits radiation and the FPD detects radiation transmitted through the patient irradiated intermittently whenever the X-ray tube and FPD move every pitch. X-ray images O1, O2, . . . , OI, . . . , and OM are decomposed for every pitch noted above. The decomposed images are composed for each projection angle to obtain projection images P1, P2 and so on. Therefore, a sectional image with a long field of view in the longitudinal direction can be obtained by carrying out a reconstruction process based on the composed projection images.

Abstract: A radiographic apparatus obtains lag-free radiation detection signals with lag-behind parts removed from radiation detection signals taken from a flat panel X-ray detector as X rays are emitted from an X-ray tube. The lag-behind parts are removed by a recursive computation on an assumption that the lag-behind part included in each X-ray detection signal is due to an impulse response formed of exponential functions, N in number, with different attenuation time constants. X-ray images are created from the lag-free radiation detection signals.

Abstract: A radiographic apparatus removes lag-behind parts from radiation detection signals taken from an FPD as X rays are emitted from an X-ray tube, on an assumption that the lag-behind part included in each X-ray detection signal is due to an impulse response formed of a plurality of exponential functions with different attenuation time constants. When a single attenuation time constant and intensity are provisionally set, checking is made whether an attenuation to a noise level of X-ray detection signals occurs in an X-ray non-emission state following an X-ray emission state. When the set attenuation time constant and intensity are found appropriate (OK), the impulse response having the single exponential function is determined valid. Corrected radiation detection signals are obtained by removing the lag-behind parts using the impulse response determined.

Abstract: In the radiographic apparatus according to this invention, when a radiographic mode designator 16 designates a non-standard radiographic mode, a signal corrector 15 uses defect information stored in one of non-standard image defect information memories 18B–18E for correcting X-ray detection signals outputted from an FPD 2. Since the pixel defect information for non-standard X-ray images is acquired by a pixel defect information converter 19 through a conversion from defect information for standard X-ray images stored in a standard image defect information memory 18A, it is unnecessary to collect output signals for pixel defect information acquisition from the FPD 2 all over again. As a result, abnormal X-ray detection signals due to defects of radiation detecting elements may be corrected promptly, regardless of how the radiation detecting elements are assigned to the pixels in the X-ray images.

Abstract: In the radiographic apparatus according to this invention, when a radiographic mode designator 16 designates a non-standard radiographic mode, a signal corrector 15 uses defect information stored in one of non-standard image defect information memories 18B-18E for correcting X-ray detection signals outputted from an FPD 2. Since the pixel defect information for non-standard X-ray images is acquired by a pixel defect information converter 19 through a conversion from defect information for standard X-ray images stored in a standard image defect information memory 18A, it is unnecessary to collect output signals for pixel defect information acquisition from the FPD 2 all over again. As a result, abnormal X-ray detection signals due to defects of radiation detecting elements may be corrected promptly, regardless of how the radiation detecting elements are assigned to the pixels in the X-ray images.

Abstract: A shielding plate is made of a conductive material connected to a ground. The shielding plate is arranged between a photo timer for measuring an amount of the radiation and a radiation-sensitive semiconductor thick film over an entire surface of an effective area for X-ray detection. The shielding plate shields a radiation noise from the photo timer, and thus the radiation noise can be released by connecting the shielding plate to the ground. As a result, the radiation noise from the photo timer which has influence on the radiation detector can be reduced.

Abstract: A subtraction image is obtained, by a subtraction process (DSA process), from a live image and a mask image. A lag-behind part included in each X-ray detection signal is considered due to an impulse response formed of exponential functions. The lag-behind part is removed from each X-ray detection signal by a recursive computation to obtain a corrected X-ray detection signal. The live image and mask image are obtained from such corrected detection signals.

Abstract: A radiographic apparatus removes lag-behind parts from radiation detection signals taken from an FPD as X rays are emitted from an X-ray tube, on an assumption that the lag-behind part included in each X-ray detection signal is due to an impulse response formed of a plurality of exponential functions with different attenuation time constants. The lag-behind parts are removed by using impulse responses of the FPD corresponding, for example, to an X-ray dose used in a fluoroscopic image pickup and an X-ray dose used in a radiographic image pickup. X-ray images are created from corrected radiation detection signals with the lag-behind parts removed therefrom.

Abstract: A radiographic apparatus removes lag-behind parts from radiation detection signals taken from an FPD as X rays are emitted from an X-ray tube, on an assumption that the lag-behind part included in each X-ray detection signal is due to an impulse response formed of a plurality of exponential functions with different attenuation time constants. When a single attenuation time constant and intensity are provisionally set, checking is made whether an attenuation to a noise level of X-ray detection signals occurs in an X-ray non-emission state following an X-ray emission state. When the set attenuation time constant and intensity are found appropriate (OK), the impulse response having the single exponential function is determined valid. Corrected radiation detection signals are obtained by removing the lag-behind parts using the impulse response determined.

Abstract: A radiographic apparatus obtains lag-free radiation detection signals with lag-behind parts removed from radiation detection signals taken from a flat panel X-ray detector as X rays are emitted from an X-ray tube. The lag-behind parts are removed by a recursive computation on an assumption that the lag-behind part included in each X-ray detection signal is due to an impulse response formed of exponential functions, N in number, with different attenuation time constants. X-ray images are created from the lag-free radiation detection signals.

Abstract: A TFT array is formed on a glass substrate (step P1). A surface protection layer is formed on the glass substrate so as to cover the TFT array (step P2). The glass substrate is divided to form active matrix, substrates with the surface protection layer being provided (step P3). The divided active matrix substrate is chamfered along its edges (step P4). The surface protection layer is removed from the active matrix substrate (step P5). An X-ray conductive layer is formed on the TFT array where the surface protection layer has been removed (step P6). By these steps, pollutants produced during the division and chamfering of the glass substrate are prevented from polluting the TFT array and the X-ray conductive layer, and the active element array and the semiconductor layer is prevented from deteriorating in terms of performance in manufacturing process for a two-dimensional image detector.

Abstract: A TFT array is formed on a glass substrate (step P1) A surface protection layer is formed on the glass substrate so as to cover the TFT a-ray (step P2). The glass substrate is divided to form active matrix substrates with the surface protection layer being provided (step P3). The divided active matrix substrate is chamfered along its edges (step P4). The surface protection layer is removed from the active matrix substrate (step P5). An X-ray conductive layer is formed on the TFT array where the surface protection layer has been removed (step P6). By these steps, pollutants produced during the division and chamfering of the glass substrate are prevented from polluting the TFT array and the X-ray conductive layer, and the active element array and the semiconductor layer is prevented from deteriorating in terms of performance in manufacturing process for a two-dimensional image detector.