Abstract: According to one embodiment, a sensitivity correction method includes acquiring count rates for respective pixels in a photon counting detector; preparing incident dose adjustment materials for the respective pixels based on the count rates for the respective pixels; and providing the incident dose adjustment materials in a surface of the photon counting detector.

Abstract: According to one embodiment, an X-ray computed tomography apparatus includes an X-ray tube and an X-ray detector. The X-ray tube generates X-rays. The X-ray detector includes a first detection area detecting the X-rays and a second detection area detecting the X-rays. The first detection area includes a first scintillator having a first fluorescence decay time, the second detection area includes a second scintillator having a second fluorescence decay time shorter than the first fluorescence decay time. The second detection area is arranged at both ends of the first detection area with respect to a channel direction.

Abstract: According to one embodiment, a sensitivity correction method includes acquiring count rates for respective pixels in a photon counting detector; preparing incident dose adjustment materials for the respective pixels based on the count rates for the respective pixels; and providing the incident dose adjustment materials in a surface of the photon counting detector.

Abstract: An X-ray CT apparatus according to an embodiment includes an X-ray tube, a photon counting detector, and a processing circuitry. The X-ray tube is configured to generate X-rays. The photon counting detector includes a plurality of detecting elements each configured to output a signal in response to any of the X-rays becoming incident thereto after having passed through an examined subject. The processing circuitry is configured to determine, within a reconstruction region, a first region on which a spectrum reconstructing process is to be performed and a second region on which an energy integral reconstructing process is to be performed, on the basis of output values related to energy spectra based on the signals output by the detecting elements. The processing circuitry is configured to generate an image on the basis of the determined first region and the determined second region.

Abstract: A photon counting detector of an embodiment includes X-ray detection elements, a capacitor, and generating circuitry. The X-ray detection elements detect an X-ray and generate an electrical signal. The capacitor is provided for each of the X-ray detection element, and accumulates an electrical signal generated in each of the X-ray detection element. The generating circuitry has low sensitivity to radiation, and generates a digital signal by using an accumulation result of the electrical signal in the capacitors, and reference information that is stored in advance.

Abstract: A photon-counting X-ray computed tomography (CT) apparatus according to an embodiment includes an X-ray tube, a detector, a photon counting circuitry, a correcting circuitry, and a calculating circuitry. The X-ray tube irradiates a subject with X-rays. The detector includes a plurality of detection elements that detect photons of X-rays incident on the detection elements. The photon counting circuitry counts the count of X-ray photons for each energy bin set in an X-ray energy distribution, for each position of the X-ray tube, and for each of the detection elements. The correcting circuitry corrects the count of the X-ray photons counted by the photon counting circuitry, based on a detection characteristic, of the detection elements. The calculating circuitry calculates the reliability of a pixel in a reconstruction image, based on the correction.

Abstract: An X-ray computer tomography (CT) apparatus according to an embodiment includes an X-ray source, an X-ray detector, and generating circuitry. The X-ray source radiates X-rays. The X-ray detector includes a scintillator including a first region close to the X-ray source and a second region distant from the X-ray source, an optical sensor that detects scintillator light obtained by converting the X-rays radiated from the X-ray source with the scintillator, and a variable layer that is provided in the scintillator and switchable between a first state in which the variable layer transmits the scintillator light between the first region and the second region and a second state in which the variable layer does not transmit the scintillator light between the first region and the second region. The generating circuitry generates a CT image based on a signal output from the X-ray detector.

Abstract: According to one embodiment, a photon counting imaging apparatus includes an X-ray tube, an X-ray detector, and data acquisition circuitry. The X-ray detector includes a detector pixel including photoelectric conversion cells each configured to individually generate an electrical signal of a predetermined pulse height, and output circuitry configured to generate an energy signal having a pulse height corresponding to energy of the X-rays based on the electrical signals from the photoelectric conversion cells. The data acquisition circuitry corrects the energy signal based on a relationship between an amplification factor and an applied voltage to the detector pixel during a period until the voltage applied to the detector pixel recovers from a breakdown voltage to a reverse bias voltage.

Abstract: According to one embodiment, an X-ray computed tomography apparatus includes an X-ray tube and an X-ray detector. The X-ray tube generates X-rays. The X-ray detector includes a first detection area detecting the X-rays and a second detection area detecting the X-rays. The first detection area includes a first scintillator having a first fluorescence decay time, the second detection area includes a second scintillator having a second fluorescence decay time shorter than the first fluorescence decay time. The second detection area is arranged at both ends of the first detection area with respect to a channel direction.

Abstract: An X-ray CT apparatus according to an embodiment includes an X-ray tube, a photon counting detector, and a processing circuitry. The X-ray tube is configured to generate X-rays. The photon counting detector includes a plurality of detecting elements each configured to output a signal in response to any of the X-rays becoming incident thereto after having passed through an examined subject. The processing circuitry is configured to determine, within a reconstruction region, a first region on which a spectrum reconstructing process is to be performed and a second region on which an energy integral reconstructing process is to be performed, on the basis of output values related to energy spectra based on the signals output by the detecting elements. The processing circuitry is configured to generate an image on the basis of the determined first region and the determined second region.

Abstract: A photon counting detector of an embodiment includes X-ray detection elements, a capacitor, and generating circuitry. The X-ray detection elements detect an X-ray and generate an electrical signal. The capacitor is provided for each of the X-ray detection element, and accumulates an electrical signal generated in each of the X-ray detection element. The generating circuitry has low sensitivity to radiation, and generates a digital signal by using an accumulation result of the electrical signal in the capacitors, and reference information that is stored in advance.

Abstract: According to one embodiment, a photon counting imaging apparatus includes an X-ray tube, an X-ray detector, and data acquisition circuitry. The X-ray detector includes a detector pixel including photoelectric conversion cells each configured to individually generate an electrical signal of a predetermined pulse height, and output circuitry configured to generate an energy signal having a pulse height corresponding to energy of the X-rays based on the electrical signals from the photoelectric conversion cells. The data acquisition circuitry corrects the energy signal based on a relationship between an amplification factor and an applied voltage to the detector pixel during a period until the voltage applied to the detector pixel recovers from a breakdown voltage to a reverse bias voltage.

Abstract: A photon-counting X-ray computed tomography (CT) apparatus according to an embodiment includes an X-ray tube, a detector, a photon counting circuitry, a correcting circuitry, and a calculating circuitry. The X-ray tube irradiates a subject with X-rays. The detector includes a plurality of detection elements that detect photons of X-rays incident on the detection elements. The photon counting circuitry counts the count of X-ray photons for each energy bin set in an X-ray energy distribution, for each position of the X-ray tube, and for each of the detection elements. The correcting circuitry corrects the count of the X-ray photons counted by the photon counting circuitry, based on a detection characteristic, of the detection elements. The calculating circuitry calculates the reliability of a pixel in a reconstruction image, based on the correction.

Abstract: An X-ray computer tomography (CT) apparatus according to an embodiment includes an X-ray source, an X-ray detector, and generating circuitry. The X-ray source radiates X-rays. The X-ray detector includes a scintillator including a first region close to the X-ray source and a second region distant from the X-ray source, an optical sensor that detects scintillator light obtained by converting the X-rays radiated from the X-ray source with the scintillator, and a variable layer that is provided in the scintillator and switchable between a first state in which the variable layer transmits the scintillator light between the first region and the second region and a second state in which the variable layer does not transmit the scintillator light between the first region and the second region. The generating circuitry generates a CT image based on a signal output from the X-ray detector.

Abstract: To solve the problems described above, an X-ray computed tomography apparatus includes an X-ray tube, a scintillator, a photoelectric convertor, a thermal storage material, a rotating portion, a rotating mechanism, and image generating circuitry. The X-ray tube generates an X-ray. The scintillator converts the X-ray generated by the X-ray tube into light. The photoelectric convertor generates an electric signal based on the light obtained by conversion by the scintillator. The thermal storage material is attached to the photoelectric convertor, and absorbs heat. To the rotating portion, the X-ray tube, the scintillator, the photoelectric convertor, and the thermal storage material are attached. The rotating mechanism rotates the rotating portion around a subject. The image generating circuitry generates an image based on the electric signal generated by the photoelectric convertor.

Abstract: A portable ultrasound diagnosis apparatus includes: an ultrasound probe that transmits and receives an ultrasound wave to and from a subject; a processing unit being connected to the ultrasound probe and including a generating unit that generates image data of the subject on the basis of an ultrasound signal received by the ultrasound probe; a display controlling unit that exercises control so as to cause the image data to be displayed by an information terminal being connected to the processing unit and having a display unit; and an identifying unit that performs an identifying process on the basis of identification information of the information terminal. The display controlling unit exercises control so that the information terminal displays a diagnosis image area while varying the size thereof relative to the size of the display unit, in accordance with a result of the identifying process by the identifying unit.

Abstract: A portable ultrasound diagnosis apparatus includes: an ultrasound probe that transmits and receives an ultrasound wave to and from a subject; a processing unit being connected to the ultrasound probe and including a generating unit that generates image data of the subject on the basis of an ultrasound signal received by the ultrasound probe; a display controlling unit that exercises control so as to cause the image data to be displayed by an information terminal being connected to the processing unit and having a display unit; and an identifying unit that performs an identifying process on the basis of identification information of the information terminal. The display controlling unit exercises control so that the information terminal displays a diagnosis image area while varying the size thereof relative to the size of the display unit, in accordance with a result of the identifying process by the identifying unit.

Abstract: A diagnostic apparatus for diagnosing the circulatory system of a patient, including an X-ray diagnostic system and an ultrasonic diagnostic system. The ultrasonic diagnostic system has an ultrasonic catheter for insertion into the circulatory systems of the patient and for scanning a circulatory organ with an ultrasonic wave to thereby an ultrasonic tomogram. A roadmap image is obtained prior to the ultrasonic diagnosis. When the ultrasonic catheter is inserted into the circulatory system of the patient, the X-ray diagnosis is performed to obtain a live image of the circulatory system which includes a picture of the catheter and is displayed overlapped on the roadmap image. The ultrasonic catheter is inserted into the circulatory system of the patient while the location of the catheter is monitored from the overlapped display of the live image and the roadmap image.