Abstract: Each semiconductor radiation detector used for a nuclear medicine diagnostic apparatus (PET apparatus) is constructed with an anode electrode A facing a cathode electrode C sandwiching a CdTe semiconductor member S which generates charge through interaction with ?-rays. Then, a thickness t of the semiconductor member S sandwiched between these mutually facing anode electrode A and cathode electrode C is set to 0.2 to 2 mm. Furthermore, the devices are mounted (laid out) on substrates in such a way that the distance (distance of conductor) between the semiconductor radiation detector and an analog ASIC which processes the signal detected by this detector is shortened. Furthermore, the substrates on which the detectors are mounted are housed in a housing as a unit (detector unit).

Abstract: A radiological imaging apparatus of the present invention includes an X-ray source for emitting an X-ray, a ?-ray detecting section for outputting a detection signal of a ?-ray, and an X-ray detecting section for outputting a detecting signal of an X-ray. The X-ray source moves around a bed for placing an examinee. The ?-ray detecting section has a plurality of radiation detectors aligned in the longitudinal direction of the bed and placed around the bed. The X-ray detecting section is positioned in a region formed between one end and the other end of the ?-ray detecting section in the longitudinal direction of the bed. The X-ray source is also positioned in the region. Since the X-ray detecting section is placed in the region, it is possible to accurately combine a PET image and an X-ray computed tomographic image.

Abstract: In a gamma camera, a plurality of radiation detector elements having a rod-shaped first electrode, a semiconductor device surrounds the first electrode to contact with it for entering a radiation, and a second electrode provided for the side surface of the semiconductor device are detachably attached to a holding member. The holding member has a first electrode contact portion contacted with the first electrode and a second electrode contact portion contacted with the second electrode. A collimator in which a plurality of radiation paths provided corresponding to the plurality of radiation detector elements are formed is arranged on the radiation entering side of the plurality of radiation detector elements. A ?-ray detection signal outputted from the first electrode contact portion is sent to a signal processing integrated circuit. A high voltage is applied to the second electrode via the second electrode contact portion.

Abstract: In a gamma camera, a plurality of radiation detector elements having a rod-shaped first electrode, a semiconductor device surrounds the first electrode to contact with it for entering a radiation, and a second electrode provided for the side surface of the semiconductor device are detachably attached to a holding member. The holding member has a first electrode contact portion contacted with the first electrode and a second electrode contact portion contacted with the second electrode. A collimator in which a plurality of radiation paths provided corresponding to the plurality of radiation detector elements are formed is arranged on the radiation entering side of the plurality of radiation detector elements. A ?-ray detection signal outputted from the first electrode contact portion is sent to a signal processing integrated circuit. A high voltage is applied to the second electrode via the second electrode contact portion.

Abstract: A radiological imaging apparatus of the present invention comprises an image pickup device and a medical examinee holding device that is provided with a bed. The image pickup device includes a large number of radiation detectors and radiation detector support plates. A large number of radiation detectors are mounted around the circumference of a through-hole and arranged in the axial direction of the through-hole. The radiation detectors are arranged in three layers formed radially with respect to the center of the through-hole and mounted on the lateral surfaces of the radiation detector support plates. Since the radiation detectors are not only arranged in the axial direction and circumferential direction of the through-hole but also arrayed in the radial direction, it is possible to obtain accurate information about a ?-ray arrival position in the radial direction of the through-hole (the positional information about a radiation detector from which a ?-ray image pickup signal is output).

Abstract: An X-ray CT apparatus having X-ray irradiator for irradiating an X-ray to an object to be inspected, an X-ray sensor for detecting an X-ray passed through the object to be inspected, an X-ray sensor signal processing circuit for processing an output signal from the X-ray sensor, and a CT control apparatus for reconstructing an image of the object to be inspected on the basis of an output signal of the X-ray sensor processed by the X-ray sensor signal processing circuit. The X-ray sensor signal processing circuit removes a DC component from the output signal of the X-ray sensor and integrates the output signal of the X-ray sensor having the DC component removed therefrom.

Abstract: A liposome containing a hydrophobic iodine compound such as a 1,3,5-triiodobenzene derivative having at least one substituent containing 18 or more carbon atoms as a membrane component, and an X-ray contrast medium containing the liposome for use in radiography of a vascular disease and the like.

Abstract: A ?-ray signal processing section 60? determines a detection time of a ? ray based on a ?-ray detection signal outputted from a semiconductor radiation detector for detecting the ? ray, and determines the energy of the ? ray. Then, a time correction circuit 70 obtains, based on the energy of the ? ray, a detection value of the detection time that corresponds to the energy of the ? ray from a time correction table indicating the relationship between the energy of the ? ray and the correction value of the detection time of the ? ray, and corrects the detection time according to the obtained correction value of the detection time. Coincidence counting is performed on the ? ray in a coincidence counting circuit 80 based on the corrected detection time.

Abstract: A radiological imaging apparatus of the present invention includes an X-ray source for emitting an X-ray, a ?-ray detecting section for outputting a detection signal of a ?-ray, and an X-ray detecting section for outputting a detecting signal of an X-ray. The X-ray source moves around a bed for placing an examinee. The ?-ray detecting section has a plurality of radiation detectors aligned in the longitudinal direction of the bed and placed around the bed. The X-ray detecting section is positioned in a region formed between one end and the other end of the ?-ray detecting section in the longitudinal direction of the bed. The X-ray source is also positioned in the region. Since the X-ray detecting section is placed in the region, it is possible to accurately combine a PET image and an X-ray computed tomographic image.

Abstract: The image pickup apparatus of the radiological imaging apparatus of the present invention includes many detector units, a ring-shaped detector support member and an X-ray source circumferential transport apparatus. Each of the detector units is attached to the detector support section in a detachable manner. A plurality of radiation detectors provided for the detector units are arranged in three layers in the radius direction of the detector support member and in three columns in the axial direction of the detector support member. Since the radiation detectors are arranged in three layers in the radius direction, it is possible to recognize the detection position of radiation in the radius direction in detail. Furthermore, since the detector units are attached in a detachable manner, it is easy to replace damaged radiation detectors.

Abstract: A radiological imaging apparatus of the present invention includes an X-ray source for emitting an X-ray, a ?-ray detecting section for outputting a detection signal of a ?-ray, and an X-ray detecting section for outputting a detecting signal of an X-ray. The X-ray source moves around a bed for placing an examinee. The ?-ray detecting section has a plurality of radiation detectors aligned in the longitudinal direction of the bed and placed around the bed. The X-ray detecting section is positioned in a region formed between one end and the other end of the ?-ray detecting section in the longitudinal direction of the bed. The X-ray source is also positioned in the region. Since the X-ray detecting section is placed in the region, it is possible to accurately combine a PET image and an X-ray computed tomographic image.

Abstract: A radiological imaging apparatus allowing semiconductor radiation detectors to be easily replaced with new ones and densely arranged. Terminals (31cjk) and (33cjk) are provided on a bottom surface of a detector aggregate (40mn) including a plurality of semiconductor radiation detectors (1); the terminals is connected to electrodes (3 and 4) of the detectors (1). A plurality of zero insertion force connectors (56) are provided on a connecting device (33jk) installed on a support substrate (32h). The terminals (31cjk and 33cjk) are detachably attached to the zero insertion force connectors (56) to mount the detector aggregates (40mn) that are the semiconductor radiation detectors (1), on the support substrate (32h). When the detector aggregates (40mn) are attached to the zero insertion force connectors (56), since no frictional force acts on the terminals, the size of the gap between the detector aggregates (40mn) is reduced.

Abstract: A radiological imaging apparatus of the present invention comprises an image pickup device and a medical examinee holding device that is provided with a bed. The image pickup device includes a large number of radiation detectors and radiation detector support plates. A large number of radiation detectors are mounted around the circumference of a through-hole and arranged in the axial direction of the through-hole. The radiation detectors are arranged in three layers formed radially with respect to the center of the through-hole and mounted on the lateral surfaces of the radiation detector support plates. Since the radiation detectors are not only arranged in the axial direction and circumferential direction of the through-hole but also arrayed in the radial direction, it is possible to obtain accurate information about a ?-ray arrival position in the radial direction of the through-hole (the positional information about a radiation detector from which a ?-ray image pickup signal is output).

Abstract: The present invention provides a semiconductor radiation detector and radiation detection apparatus capable of improving energy resolution and the semiconductor radiation detection apparatus includes a semiconductor radiation detector and a signal processing circuit which processes a radiation detection signal output from the semiconductor radiation detector. The semiconductor radiation detector is provided with anode electrodes A and cathode electrodes C disposed so as to face each other with semiconductor radiation detection elements placed in-between. The semiconductor radiation detection element is made up of a single crystal of thallous bromide containing trivalent thallium (e.g., tribromobis thallium). The semiconductor radiation detector containing such a semiconductor radiation detection element reduces lattice defects in the single crystal and thereby increases charge collection efficiency.

Abstract: Disclosed herein is a radiation imaging apparatus and radiation-imaging-apparatus-based nuclear medicine diagnosis apparatus having a collimator in which a plurality of rectangular through-holes are arranged in a grid pattern and separated by septa is rotated through a predetermined angle as viewed from above in relation to the layout of a plurality of rectangular detectors that are arranged in a grid pattern. The predetermined angle ranges from 20 to 70 degree and more preferably from 30 deg to 60 deg. With this configuration, the influence of sensitivity variations (moire patterns) that are included in an image picked up due to interference with a collimator when pixel type detectors are used is eliminated.

Abstract: A compound represented by the following general formula (IA) or a salt thereof: wherein Ar1 represents hydrogen atom or an aryl group having at least one iodine atom as a substituent; Ar2 represents an aryl group having at least one iodine atom as a substituent; L1 and L2 independently represent a divalent bridging group of which main chain contains 6 or more carbon atoms; L3 represents a single bond or a divalent bridging group of which main chain contains 1 to 6 carbon atoms and one oxygen atom; X represents a functional group containing at least one heteroatom, provided that, when L3 is a single bond, X represents a functional group other than hydroxyl group. The compound can be used as a membrane component of liposomes, and the liposomes can be used as a contrast medium for X-ray radiography.

Abstract: A liposome containing a hydrophobic iodine compound represented by the following general formula (I) as a membrane component: R1—CO2—R2 wherein R1 represents a substituted or unsubstituted 2,3,5-triiodophenyl group or a substituted or unsubstituted 3,4,5-triiodophenyl group; and R2 represents a hydrocarbon group having 10 or more carbon atoms, and an X-ray contrast medium, which comprises said liposome which is used for radiography of a vascular disease.

Abstract: In a radiological imaging apparatus, a radiation detecting section includes semiconductor detectors arranged in four columns and four rows. Each of the semiconductor detectors includes a semiconductor base material, and an anode electrode film (first electrode film) and a cathode electrode film (second electrode film) lying opposite each other so as to sandwich the semiconductor base material between them. A first conductive member is installed on each first electrode film. Second electrode films of four semiconductor detectors within a row are connected together using one second conductive member. A shaping amplifier connected to the first conductive members with a wire executes a waveform shaping process using a shaping time shorter than that of a shaping amplifier connected to the second conductive member with a wire; the first conductive members are provided for the four semiconductor detectors within a column.

Abstract: An X-ray CT apparatus having X-ray irradiator for irradiating an X-ray to an object to be inspected, an X-ray sensor for detecting an X-ray passed through the object to be inspected, an X-ray sensor signal processing circuit for processing an output signal from the X-ray sensor, and a CT control apparatus for reconstructing an image of the object to be inspected on the basis of an output signal of the X-ray sensor processed by the X-ray sensor signal processing circuit. The X-ray sensor signal processing circuit removes a DC component from the output signal of the X-ray sensor and integrates the output signal of the X-ray sensor having the DC component removed therefrom.

Abstract: An image pickup apparatus of a radiological imaging apparatus includes a plurality of radiation detectors arranged in a ring form around a through hole section formed on a casing into which an examinee is inserted. An X-ray source unit having an X-ray source moves in a circumferential direction of the through hole section along a ring-shaped guide rail provided on the casing. Each radiation detector outputs both an X-ray detection signal which is a detection signal of X-rays that have passed through the examinee and a ?-ray detection signal which is a detection signal of ?-rays radiated from the examinee caused by radiopharmaceutical. A computer creates an X-ray computed tomographic image data based on the X-ray detection signal and a PET image data based on the ?-ray detection signal and creates fused tomographic image data using the X-ray computed tomographic image data and the PET image data.