WO2006077869A1 - Systeme ct a rayons x - Google Patents

Systeme ct a rayons x Download PDF

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Publication number
WO2006077869A1
WO2006077869A1 PCT/JP2006/300618 JP2006300618W WO2006077869A1 WO 2006077869 A1 WO2006077869 A1 WO 2006077869A1 JP 2006300618 W JP2006300618 W JP 2006300618W WO 2006077869 A1 WO2006077869 A1 WO 2006077869A1
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Prior art keywords
imaging
ray
periodic motion
calculated
motion
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PCT/JP2006/300618
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English (en)
Japanese (ja)
Inventor
Hiroto Kokubun
Osamu Miyazaki
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Hitachi Medical Corporation
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Priority to JP2006553920A priority Critical patent/JPWO2006077869A1/ja
Publication of WO2006077869A1 publication Critical patent/WO2006077869A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computerised tomographs
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/50—Clinical applications
    • A61B6/503—Clinical applications involving diagnosis of heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • A61B6/541—Control of apparatus or devices for radiation diagnosis involving acquisition triggered by a physiological signal

Definitions

  • the present invention relates to a period from a periodic motion detection device such as an electrocardiograph and a respiration sensor that measures a periodic motion of a portion of a subject that repeats periodic motion such as the heart and lungs (hereinafter referred to as a periodic motion portion).
  • the present invention relates to an improvement in an X-ray CT apparatus equipped with a periodic motion measurement device that takes a tomographic image of a periodic motion site using a signal waveform representing motion.
  • This application is a patent application claiming priority based on Japanese Patent Application No. 2005-009731 based on the Japanese Patent Law, and is incorporated by reference in order to enjoy the benefits of Japanese Patent Application No. 2005-009731. It is an application to receive.
  • Patent Document 1 when imaging a periodic motion region of a subject using an X-ray CT apparatus, as shown in Patent Document 1, while measuring the periodic motion of the periodic motion region with a periodic motion measurement device, Scan the X-ray CT device in synchronization with the phase of the signal waveform representing motion, or select and process the scan data of the X-ray CT device in synchronization with the phase of the signal waveform representing periodic motion. It was used for reconstruction of tomographic images.
  • Patent Document 1 Japanese Patent Laid-Open No. 2002-330961
  • An object of the present invention is to obtain imaging data sufficient to suppress exposure to a subject and to reconstruct a whole image of a desired imaging range in a certain motion cycle of a target periodic motion site. It is to provide an X-ray CT apparatus capable of performing the above. Disclosure of the invention
  • the X-ray CT apparatus of the present invention includes an X-ray source for irradiating a subject and the X-ray source with the subject sandwiched between the X-ray source.
  • An X-ray detector disposed opposite to the X-ray detector for detecting transmitted X-rays of the subject, a rotary ring mounted with the X-ray source and the X-ray detector and capable of rotating around the subject, A cross-section of the periodic motion region of the subject based on the table on which the subject is mounted and movable in the body axis direction of the subject and the transmitted X-ray data of the subject acquired by the X-ray detector
  • An X-ray CT apparatus comprising: an image processing device that creates an image; and a display device that displays a tomographic image created by the image processing device, the measurement terminal being attached to the subject and the subject Measure the waveform signal of periodic motion from the periodic motion part of the specimen, and the measured waveform signal is In an X-ray
  • a motion cycle of at least one of the start or end of X-ray exposure from the X-ray source is set, and at least one of the start or end of X-ray exposure corresponding to the set motion cycle, the X-ray exposure from the X-ray source
  • a control unit that controls the X-ray irradiation, acquisition of the imaging data by the X-ray detector, the moving speed of the table, and rotation of a rotating ring to execute imaging.
  • the X-ray CT apparatus and the subject are equipped with measurement terminals, and waveform signals representing the periodic motion of the periodic motion site force of the subject are measured and measured.
  • the image processing device represents the periodic motion from the periodic motion measurement device prior to the start of imaging.
  • This shooting start Based on the reference point timing, it has a timing calculation unit that predicts and calculates the timing at which the desired phase of the desired periodic motion appears for the periodic motion part as the imaging start target phase timing.
  • the control unit controls the start of X-ray exposure from the X-ray source of the X-ray CT apparatus based on the imaging start target phase timing acquired from the timing calculation unit, and this timing calculation unit further prior to the end of imaging.
  • the motion period of the periodic motion part is calculated based on the waveform signal representing the periodic motion of the periodic motion part measured by the periodic motion measuring device during imaging, and
  • the timing at which the feature point appears is predicted and calculated as the imaging end preparation reference point timing, and the periodic motion part is imaged based on the imaging end preparation reference point timing.
  • the timing at which the target phase of the desired periodic motion appears is predicted and calculated as the imaging end target phase timing, and the control device detects the X-ray exposure from the X-ray source based on the acquired imaging end target phase timing. It is characterized by controlling the end of shooting.
  • FIG. 1 is a schematic configuration diagram of an X-ray CT apparatus provided with a periodic motion measuring apparatus for a subject according to the present invention.
  • FIG. 2 is an explanatory diagram of an electrocardiogram waveform.
  • FIG. 3 is a diagram for explaining the range specified by the position in the body axis direction of the tomographic image reconstructed by the imaging data captured in synchronization with the phase of the R wave of the electrocardiogram waveform.
  • Fig. 4 shows image data taken in synchronization with the phase of the R wave of the electrocardiogram waveform when the electrocardiogram waveform is disturbed, and the tomographic image reconstructed by this data in the direction of the body axis. The figure explaining the range specified by the position.
  • FIG. 5 is the same ECG waveform timing as in FIG. 3, and is taken in synchronization with the phase of the ECG waveform R—R 50%, and the body axis direction of the tomographic image reconstructed by this data The figure explaining the range specified by the position of.
  • FIG. 6 is a flowchart for explaining the procedure of processing for the end of the imaging start force of the heart synchronized with the electrocardiographic waveform and the subsequent image reconstruction according to one embodiment of the present invention.
  • FIG. 7 is a diagram for explaining the timing determination of imaging start (X-ray ON) in synchronization with the R wave phase (RR 100%) of an electrocardiographic waveform according to one embodiment of the present invention.
  • FIG. 8 is a diagram for explaining the determination of the start timing of imaging in synchronization with the phase of the electrocardiographic waveform R—R 50% according to one embodiment of the present invention.
  • FIG. 9 illustrates the determination of the timing of the start of imaging in synchronization with the R wave phase of the electrocardiographic waveform according to one embodiment of the present invention when an arrhythmia occurs in the electrocardiographic waveform before the start of imaging.
  • FIG. 10 is a diagram for explaining the timing determination at the end of imaging (X-ray OFF) synchronized with the R wave phase (R-R 100%) of the electrocardiographic waveform according to one embodiment of the present invention.
  • FIG. 11 is a diagram for explaining timing determination of the end of imaging in synchronization with the phase of an electrocardiographic waveform R—R 70% according to one embodiment of the present invention.
  • FIG. 12 is a diagram for explaining the determination of the end of imaging in synchronization with the phase of the R wave of the electrocardiographic waveform when an arrhythmia occurs in the electrocardiographic waveform before the end of imaging.
  • FIG. 1 shows a configuration of an X-ray CT apparatus according to the present embodiment.
  • 1 is an X-ray tube
  • 2 is a scanner gantry
  • 3 is an object table
  • 4 is an X-ray detector
  • 5 is a display device
  • 6 is an electrocardiograph as a periodic motion measurement means.
  • 7 is an image processing device
  • 8 is a rotary ring
  • 9 is a collimator
  • 10 is a rotary drive device
  • 11 is a measurement control device
  • 12 is a computer
  • 13 is an input device
  • 14 is a computer 12
  • the shooting timing calculation devices included in are shown below.
  • the scanner gantry 2 includes an X-ray tube 1 mounted on a rotating ring 8, a collimator 9 that controls the direction of the X-ray bundle attached to the X-ray tube 1 and the X-ray irradiation field (range), and a rotating ring 8
  • the X-ray detector 4 installed in the X-rays are irradiated from the X-ray tube 1, pass through the subject, and detected by the X-ray detector 4. At this time, as the rotating ring 8 rotates, X-ray transmission imaging data is collected from around the subject.
  • the image processing device 7 creates imaging data from the measurement data detected by the X-ray detector 4 and calculates a CT image signal from the imaging data.
  • the display device 5 displays and outputs the CT image signal as a CT image.
  • the rotating ring 8 is driven to rotate by the rotation driving device 10. Further, the rotational drive device 10 is controlled by the measurement control device 11 in terms of speed, drive start, stop, and the like.
  • X-ray tube 1 The X-ray irradiation range limited by the collimator 9 is also controlled by the measurement control device 11. This measurement control device 11 is controlled by a computer 12.
  • FIG. 2 shows an example of this electrical signal.
  • the electrical signal is composed of several waveform features based on cardiac motion. As shown, each feature is usually named P wave, Q wave, R wave, S wave, and T wave.
  • P wave Pulse-to-senor
  • Q wave Pulse-to-senor
  • R wave Radio wave
  • S wave S wave
  • T wave T wave
  • the heartbeat phase is often determined based on the R wave that can be detected most reliably.
  • FIG. 3 A method for reconstructing a tomographic image from imaging data collected using the heartbeat phase acquired by the electrocardiograph 6 as a parameter will be described with reference to FIG.
  • the horizontal axis is time
  • the vertical axis is the body axis position of the subject.
  • Table 3 carries the subject and sends the subject in the body axis direction.
  • the rotating ring 8 rotates to capture imaging data necessary for creating a tomographic image from around the subject.
  • the imaging data required to create a tomographic image requires an imaging angle range from at least 180 degrees, even if an opposed X-ray beam is used.
  • the range surrounded by the rectangles 31, 32, and 33 in the figure indicates the range of the captured image data.
  • the widths of the rectangles 31, 32, and 33 indicate the range of the shooting angle at which the data was taken. In this case, the shooting angle range is 180 degrees.
  • the vertical widths of the rectangles 31, 32, and 33 indicate the slice range that can be photographed, that is, the X-ray irradiation range in the slice direction. This also corresponds to the number of X-ray detector 4 columns.
  • the dotted line in the figure shows the movement trajectory of the X-ray irradiation range in the slice direction. This is consistent with the movement trajectories of the rectangles 31, 32, and 33 above.
  • the slope of the dotted line corresponds to the moving speed of Table 3.
  • an electrocardiographic waveform 20 is shown parallel to the time axis (horizontal axis).
  • the electrocardiogram waveform 20 is, for example, an ECG (Electro Cardio Gram) signal.
  • ECG Electro Cardio Gram
  • the R wave is emphasized to show the heartbeat cycle.
  • FIG. 3 reference numeral 40 denotes a body axis direction reconstruction range based on imaging data represented by rectangles 31, 32, and 33.
  • the heart scanogram 19 is drawn side by side with the reconstruction range 40 in the body axis direction.
  • the heart scanogram 19 is obtained by irradiating X-rays from one direction along the body axis of the subject prior to imaging of the subject. From this figure, it can be seen that the reconstruction range 40 of the body axis indicates that the entire region of the heart to be imaged is sufficiently included in the imaging range.
  • FIG. 4 because the heartbeat is scheduled to be disturbed and the force at which the heartbeat appears at the timing of heartbeat 27, the imaging data represented by rectangles 34, 35, and 36 are captured corresponding to 3 heartbeats 28, 29, and 30. Give an example.
  • the reconstructed range in the body axis direction reconstructed by this imaging data is shown as 41. From the acquired imaging data 34, 35, 36, the image in the range indicated by 42 in the heart scanogram 19 can be reconstructed. I will show you that.
  • FIG. 5 shows an example in which imaging data 37, 38, and 39 are captured in synchronization with the phase of the electrocardiographic waveform R—R 50% at the same timing of the electrocardiographic waveform as in FIG.
  • the range of reconstruction in the body axis direction that is reconstructed by this imaging data is indicated by 43.
  • an image in the range indicated by 44 in the scanogram 19 of the juxtaposed heart is shown. Indicates that it cannot be reconstructed. This is because the table on which the subject was placed was driven at the same timing as in Fig. 3.
  • R ⁇ R 50% indicates a heartbeat phase corresponding to a position of about 50% expressed by a relative method when the interval between adjacent R waves is 100%.
  • FIGS. 7 to 12 in accordance with FIG. 6, the heart according to one embodiment of the present invention using the combination of the electrocardiograph 6 and the X-ray CT apparatus shown in FIG. Each processing step until creating a tomographic image is explained.
  • step S100 the subject is linearly scanned from one direction in the body axis direction, and a scanogram image for determining the image creation range is photographed.
  • the imaging result obtained here is a fluoroscopic image, which serves as an index for deciding how much the subject table 3 should be sent out when imaging the target imaging region.
  • step S101 the operator inputs shooting conditions from the input device 13 and sets them.
  • the imaging conditions to be set include the rotation speed of the rotary scanner 8, table movement speed, and X-ray irradiation intensity. There is a range for creating an image using the scanogram acquired in step S100.
  • step S102 the heart rate is monitored using the electrocardiograph 6 for the purpose of predetermining the imaging start timing. That is, the ECG signal from the subject is monitored for a predetermined period using the electrocardiograph 6 shown in FIG.
  • step S103 an average one heartbeat cycle CC (Cardiac Cycle: time required for one heartbeat) of the subject is obtained from the electrocardiogram waveform monitored in step S102.
  • CC Cardiac Cycle: time required for one heartbeat
  • steps S102 and S103 corresponds to the processing in the Monitor area shown in FIGS.
  • the force for obtaining the heartbeat period and heartbeat phase of the electrocardiogram waveform using the R wave apex in the electrocardiogram waveform as a reference point P wave, Q wave, S wave, Other feature parts such as T wave may be used as the reference point.
  • step S104 the imaging timing calculation means 14 shown in FIG. 1 determines the imaging start timing 220 based on the heartbeat cycle of the subject calculated in step S103.
  • a method for calculating the photographing start timing 220 according to this embodiment will be described with reference to FIGS.
  • FIG. 7 is a diagram for explaining the timing determination of the imaging start ⁇ X-ray ON> synchronized with the R wave phase (R—R 100%) of the electrocardiographic waveform according to an embodiment of the present invention.
  • the electrocardiogram waveform 20 measured by the electrocardiograph 6 is shown in the figure, and the band below the electrocardiogram waveform 20 indicates the presence or absence of X-ray exposure.
  • Monitor is the ECG waveform monitoring
  • PrepSt is the preparation start time
  • ReconTime is the required reconstruction time
  • 201 is the top of the last R wave during ECG monitoring
  • 202 is the start of imaging
  • Reference numeral 203 indicates the peak of the R wave of the heartbeat monitored after X-ray exposure, which is also the target heartbeat phase 230
  • 220 indicates the start timing of imaging.
  • the imaging start preparation time is calculated from the following equation.
  • PrepSt Preparation time for shooting start CC: 1 heart cycle
  • Target heart rate phase (1.0 here)
  • Reconstruction-required imaging time in the expression ReconTime is an imaging time required to collect the minimum necessary data for reconstructing one tomographic image.
  • the reconstitution required imaging time ReconTime is the value of the rotating ring scanner. It corresponds to about 1/2 of the rotation time.
  • the required reconstruction time ReconTime depends on the specifications of the X-ray CT system and the reconstruction conditions, so it may be calculated in step S101 or calculated up to step S104. Also good.
  • the reconstruction of the images This is to set the capture range of the captured data so that the center position of the captured data is the target heartbeat phase.
  • the image quality of the target heartbeat phase is optimized by selecting the shooting data by matching the temporal point of the target phase with the central portion of the shooting data and reconstructing it.
  • CC is one heartbeat cycle calculated in step S103.
  • the required imaging start timing 220 is calculated by matching the middle of the reconstruction required imaging time ReconTime with the target heartbeat phase 203.
  • the measurement control device 11 of FIG. 1 operates so that the exposure is started after the imaging start preparation time Prep St obtained in (Equation 1) has elapsed, using the predicted heartbeat 202 immediately before.
  • FIG. 8 is a diagram for explaining the timing for starting imaging in synchronization with the phase of the electrocardiographic waveform R—R 50% according to one embodiment of the present invention.
  • PhaseTime Time from the reference point to the target heartbeat phase
  • Target heartbeat phase (0.5 here) Specify the target heartbeat phase to reconstruct the tomogram, and use the time from the reference point to the target heartbeat phase. (Equation 3)
  • PhaseTime Time from the reference point to the target heartbeat phase
  • the imaging start timing 220 obtained by matching the middle of the reconstruction-required imaging time ReconTime with the target heartbeat phase 230 is determined.
  • the measurement control device 11 of FIG. 1 operates so that the exposure is started after the imaging start preparation time PrepSt obtained in (Equation 3) has elapsed, with the heartbeat 202 immediately before being predicted as a trigger.
  • FIG. 9 is a diagram showing a case where the imaging start timing cannot be calculated by the method of FIG. 7 due to arrhythmia when the peak of the R wave is the target heartbeat phase.
  • Arrhythmia is a case where an out-of-cycle heartbeat occurs suddenly. If an arrhythmia appears in the ECG waveform, an error will occur in the preparation start time PrepSt, and it will not be possible to start imaging at the correct timing.
  • the timing calculation means 14 calculates the imaging start preparation time PrepSt based on the prediction reference point 202 once as described with reference to FIG. Next, the electrocardiograph 6 in FIG. 1 monitors whether there is a sudden heartbeat during the imaging start preparation time PrepSt. . When the occurrence is confirmed, the imaging timing calculation means 14 calculates the imaging start timing 220 by calculating again the imaging start preparation time PrepSt using the post-occurrence reference point 209 as the correction reference point.
  • the imaging start timing 220 obtained by matching the middle of the reconstruction required imaging time ReconTime with the target heartbeat phase 230 is determined.
  • the measurement control device 11 of FIG. 1 operates so that the exposure starts after the elapse of the imaging start preparation time PrepSt obtained by (Equation 1) using the heartbeat 209 as the immediately preceding correction reference point as a trigger.
  • step S105 the measurement controller 11 calculates the predicted reference point measurement time 202 and the imaging start preparation time PrepSt. And start shooting
  • steps S106 and S107 In parallel with the imaging after the start of imaging, in steps S106 and S107, similarly to steps S10 02 and S103 described above, monitoring of the cardiac radio wave shape necessary for calculating the imaging end timing in step S108 and based on it Calculate the heart rate cycle.
  • step S108 the imaging timing calculation means 14 shown in FIG. 1 calculates the imaging end timing based on the heartbeat cycle measured in step S107.
  • a method for calculating the photographing end timing 430 will be described with reference to FIGS.
  • FIG. 10 is a diagram for explaining the timing determination of the end of imaging ⁇ X-ray OFF> synchronized with the R wave phase (R—R 100%) of the electrocardiographic waveform according to one embodiment of the present invention.
  • the electrocardiogram waveform 20 measured by the electrocardiograph 6 is shown in the figure, and the band below the electrocardiogram waveform 20 indicates the presence or absence of X-ray exposure.
  • Monitor is the monitoring during imaging
  • PrepEd is the preparation time for completion of imaging
  • ReconTime is the imaging time required for reconstruction
  • 401 is the heart rate monitored during X-ray exposure as the peak of the R wave
  • 410 is the predicted reference point for the end of radiography, that is, the start point for preparation of radiography completion.
  • the scheduled imaging end timing calculated in advance by the timing calculation unit 14 based on the imaging range of the heart to be imaged, 402 is the target heartbeat phase 420, and the R wave of the heartbeat monitored just before the X-ray exposure ends 430 indicates the end timing of shooting.
  • step S108 first, the time at which the collection of the shooting data necessary for image reconstruction of the shooting range set in S101 is taken in as the scheduled shooting end timing 410.
  • This scheduled imaging end timing 410 is just the time when the X-ray detector 4 finishes imaging the last slice plane of the imaging range, and normal image reconstruction that does not consider scanning of ECG synchronization based on the target heart rate position. This is the necessary shooting range.
  • the time required for the detector to image the final slice position at the target heartbeat phase after the imaging end scheduled timing 410 is calculated. For this reason, by monitoring the electrocardiogram waveform, the end-of-shoot preparation reference point timing 401, which is the reference of the end-of-shoot timing 430, is predicted and calculated, and the end-of-shoot preparation time PrepEd is added to this, and the end-of-shoot timing 430 And
  • the imaging end preparation time is calculated by the following (Equation 4).
  • Target heart rate phase (1.0 here)
  • the imaging completion preparation time PrepEd in the above (Equation 4) is also applied when calculating the imaging completion preparation time PrepEd when reconstructing imaging data of all heartbeat phases between adjacent R waves.
  • the heartbeat phase to be reconstructed is determined in advance at the time of imaging, it is possible to further reduce the exposure by adjusting the ReconTime to further advance the imaging end timing 430.
  • FIG. 11 is a diagram for explaining the determination of the end timing of imaging in synchronization with the phase of the electrocardiographic waveform R—R 70% according to one embodiment of the present invention.
  • step S 108 based on the one heartbeat period obtained in step S107, a time PhaseTime from the imaging end reference point 401 to the target heartbeat phase 420 is calculated by the following (formula 5).
  • PhaseTime Time from the reference point to the target heartbeat phase
  • Reconstruction-required imaging time The reason why the half-time value of ReconTime is added to PhaseTime is that, as explained for the imaging start timing with respect to FIG. This is because the range of capturing of the photographic data is set so that the center position of the photographic data used for the configuration becomes the target heartbeat phase. In other words, if the image data is selected by matching one point on the electrocardiogram waveform of the target heartbeat phase with the central portion of the imaged data and then reconstructed, the image quality of the target heartbeat phase is optimized.
  • the shooting completion preparation time PrepEd to be added to the reference point 401 is calculated by the following equation.
  • PrepEd PhaseTime + ReconTime / 2 (o no
  • PhaseTime Time from the reference point to the target heartbeat phase
  • ReconTime Required reconstruction time Note that the scheduled end of imaging 410 is the time when the X-ray detector 4 finishes capturing the final slice plane of the imaging range, as described in FIG. 10, and is based on the target heartbeat phase. This is an imaging range necessary for normal image reconstruction that does not take into account the electronic synchronization scan. Therefore, it is only necessary that the photographing end timing 430 occurs after the scheduled photographing end timing 410.
  • FIG. 12 shows a correction change method in the case where the end of the R wave cannot be calculated by the method of FIG. 10 due to the arrhythmia when the apex of the R wave is the target heartbeat phase.
  • an error occurs in the shooting completion preparation time PrepE d, and the shooting cannot be completed at the correct timing! /.
  • the process is the same as in Fig. 10 until the preparation time for shooting end PrepEd is obtained.
  • the presence or absence of a sudden heartbeat is monitored by the electrocardiograph 6 in FIG. 1 until the reference point 402 which is also the target heartbeat position 420 is measured.
  • the imaging completion preparation time PrepEd is calculated again using the post-occurrence reference point 405 as a corrected reference point. Even when a sudden heartbeat occurs due to the above processing, the imaging can be ended at the correct imaging end timing 430.
  • step S109 the measurement control device 11 stops the X-ray exposure when the imaging end timing 430 obtained as a result of S108 arrives. Similarly, based on the measurement time of the reference point 401 obtained in step S108 and the shooting completion preparation time PrepEd, the operation of each unit necessary for shooting stop such as table movement stop is started.
  • step S110 reconstruction of imaging data acquired in synchronization with the target heartbeat phase monitored by the electrocardiograph 6 in step S106 and subsequent steps is performed.
  • the present embodiment it is possible to perform imaging at a lower exposure by appropriately setting the imaging start timing 220 and the imaging end timing 430 in synchronization with each target heartbeat phase. As a result, the exposure to the subject can be reduced, and even when non-periodic movements such as arrhythmia appear before and during imaging, minimal corrections are made to the imaging start timing 220 and imaging end timing 430. It is possible to continue and end shooting by adding
  • the periodic motion measuring device is an electrocardiograph and the heart is an imaging target.
  • the present invention can be applied to any organ that performs periodic motion in the same manner as described above.
  • the present invention can be applied to imaging of a lung field or the like.
  • the X-ray exposure timing may be provided with a predetermined time margin depending on the accuracy of scan control.

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Abstract

Dans un système CT à rayons X, équipé d'une unité de mesure à mouvement périodique, un processeur d'images comprend une partie de calcul de temporisation destinée à calculer la période de mouvement dans une partie de mouvement périodique avant le début de la prise d'images photographiques, à prévoir une temporisation de l'apparition dans le signal de mouvement périodique d'un point de trait caractéristique, qui correspond à une temporisation du point de référence de préparation à la prise d'images photographiques, et à prévoir / calculer une temporisation dans laquelle la phase cible du mouvement périodique apparaît en tant que phase cible du début de prise d'images photographiques, sur la base de la temporisation du point de référence de préparation à la prise d'images photographiques. Un contrôleur commande le début d'une exposition aux rayons X sur la base de la temporisation de phase cible du début de prise d'images photographiques, la partie de calcul de temporisation calcule la période de mouvement dans une partie de mouvement périodique avant la fin de la prise d'images photographiques, prévoit / calcule une temporisation dans laquelle un point de trait caractéristique apparaît dans le signal de mouvement périodique en tant que temporisation du point de référence de fin de prise d'images photographiques, et produit / calcule une temporisation de phase cible du mouvement périodique sur la base d'une temporisation de point de référence de préparation à la fin de prise d'images photographiques. Le contrôleur commande la fin d'une exposition aux rayons X sur la base de la temporisation de phase cible de fin de prise d'images photographiques.
PCT/JP2006/300618 2005-01-18 2006-01-18 Systeme ct a rayons x WO2006077869A1 (fr)

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JP2013169358A (ja) * 2012-02-21 2013-09-02 Toshiba Corp Ｘ線ｃｔ装置
JP2015003273A (ja) * 2014-10-08 2015-01-08 株式会社東芝 Ｘ線コンピュータ断層撮影装置
JPWO2013047439A1 (ja) * 2011-09-27 2015-03-26 株式会社日立メディコ Ｘ線ｃｔ装置及び画像補正方法
JP2016016192A (ja) * 2014-07-10 2016-02-01 株式会社日立メディコ Ｘ線ｃｔ装置
JPWO2014024857A1 (ja) * 2012-08-07 2016-07-25 株式会社日立製作所 Ｘ線ｃｔ装置およびｘ線ｃｔ装置の撮影方法
JP2016172008A (ja) * 2016-04-26 2016-09-29 東芝メディカルシステムズ株式会社 Ｘ線コンピュータ断層撮影装置
US9757075B2 (en) 2012-02-02 2017-09-12 Toshiba Medical Systems Corporation X-ray CT system
CN110037721A (zh) * 2019-04-30 2019-07-23 西门子(深圳)磁共振有限公司 X光成像设备及其操作方法

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JP2009072572A (ja) * 2007-08-29 2009-04-09 Toshiba Corp Ｘ線コンピュータ断層撮影装置および断層撮影方法
JP2010075558A (ja) * 2008-09-26 2010-04-08 Toshiba Corp Ｘ線コンピュータ断層撮影装置
JPWO2013047439A1 (ja) * 2011-09-27 2015-03-26 株式会社日立メディコ Ｘ線ｃｔ装置及び画像補正方法
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JP2016172008A (ja) * 2016-04-26 2016-09-29 東芝メディカルシステムズ株式会社 Ｘ線コンピュータ断層撮影装置
CN110037721A (zh) * 2019-04-30 2019-07-23 西门子(深圳)磁共振有限公司 X光成像设备及其操作方法
CN110037721B (zh) * 2019-04-30 2023-08-04 西门子(深圳)磁共振有限公司 X光成像设备及其操作方法

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