JP2010167254A - X-ray diagnosis apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To reduce contrast imaging load of a subject in performing contrast rotary photographing twice or more times. <P>SOLUTION: This X-ray diagnosis apparatus includes: a substantially C-shaped arm 60; a support mechanism 22 rotatably supporting the substantially C-shaped arm; a rotary driving part 23 for driving the rotation of the substantially C-shaped arm; an X-ray tube 12 mounted to the substantially C-shaped arm; a high voltage generating part 26 for generating high voltage for generating X-rays from the X-ray tube; an X-ray detector 10 mounted to the substantially C-shaped arm opposite to the X-ray tube; and a rotary photographing control part 20, which controls the operation of the support mechanism, the high voltage generating part and the X-ray detector for repeating two or more times the rotary photographing operation of continuously or intermittently generating the X-rays from the X-ray tube while rotating the substantially C-shaped arm and repeating the X-ray detection by the X-ray detector after single injection of a contrast medium, and performs the time control management each of the rotary photographing operation two or more times according to the time taking the time of the single injection of the contrast medium as a starting point. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an X-ray diagnostic apparatus capable of rotational imaging, which is provided with a substantially C-shaped arm.

  There are examination techniques called CTHA (CT under hepatic arteriography) and Single level Dynamic CTA to diagnose liver tumors. This is a method of imaging a CT (computer tomography) while imaging the hepatic artery. However, despite both imaging from the same hepatic artery, these tests are usually performed with separate imaging, contributing to increased patient burden.

  On the other hand, as a rotational imaging technique, there are already two continuous rotational imaging functions after contrast medium injection. However, this imaging is only for observing the blood flow and the blood vessel shape, and does not require any precision as time control. For this reason, in the first rotational imaging, the imaging start time is set starting from the contrast injection start time, but in the second rotational imaging, the imaging start time is set starting from the first imaging end time. In order to reconstruct 3D images, it is necessary that the target area of reconstruction is continuously filled with contrast medium during imaging, and the imaging start time control requires more accuracy than imaging for observation. And In particular, the rotational imaging time changes mainly depending on the rotational speed and acceleration / deceleration time, but the rotational speed needs to be changed depending on the time during which the contrast agent stays in the reconstructed region of interest and the required image quality level. For example, the C-arm needs to be rotated at a high speed in a region where the flow is fast, such as an artery, and in order to observe a slight contrast difference, it is necessary to acquire data at a fine angular sampling pitch. It is necessary to rotate the C-arm at a low speed. Furthermore, the acceleration / deceleration time may vary depending on the tension of the belt that drives the rotation. From such a background, it is difficult to set the second imaging start time from the first imaging end time as a starting point, and as a result, the reconstruction target part is not filled with the contrast agent, or conversely There is a danger that the contrast medium is filled in advance with the contrast medium and the contrast medium has already been removed from the reconstructed area of interest at the end of imaging. This error becomes more prominent as the number of rotational shootings increases.

  An object of the present invention is to provide an interface that reduces the burden of contrast on a subject when performing two or more contrast rotation imaging and accurately and easily identifies the imaging start time after the second imaging. .

  One aspect of the present invention is mounted on the substantially C-shaped arm, a support mechanism that rotatably supports the substantially C-shaped arm, a rotation drive unit that drives rotation of the generally C-shaped arm, and the substantially C-shaped arm. An X-ray tube, a high-voltage generator for generating a high voltage for generating X-rays from the X-ray tube, and an X-ray mounted on the substantially C-arm in a direction facing the X-ray tube A single contrast agent is used for rotational imaging operation in which X-rays are continuously or intermittently generated from the X-ray tube while rotating the detector and the substantially C-shaped arm, and X-ray detection is repeated by the X-ray detector. The operation of the support mechanism, the high voltage generator, and the X-ray detector is controlled so as to be repeated a plurality of times after the injection, and each of the plurality of rotation imaging operations is performed as the single contrast agent injection. Rotation shooting control unit that performs time control management based on the time starting from To provide an X-ray diagnostic apparatus characterized by comprising a.

  According to the present invention, it is possible to reduce the contrast burden generated on the subject when performing two or more contrast rotation imaging, and to stabilize the image quality of the reconstructed image by accurately performing the second and subsequent imaging start times. As a result, it is possible to ensure adequately and to easily identify the imaging start time.

1 is a configuration diagram of an X-ray diagnostic apparatus according to a first embodiment. It is an external view of the X-ray imaging mechanism of FIG. It is a figure which shows the 1st imaging | photography procedure of 1st Embodiment. It is a figure which shows the area | region limited by the 2nd rotation imaging | photography of FIG. It is a figure which shows the 3rd imaging | photography procedure of 1st Embodiment. It is a figure which shows the 4th imaging | photography procedure of 1st Embodiment. It is a figure which shows the imaging | photography procedure of 2nd Embodiment. It is a block diagram of the X-ray diagnostic apparatus which concerns on 2nd Embodiment. FIG. 9 is a diagram showing a list display example of reduced DSA images (reduced digital subtraction angio images) for supporting setting of the contrast medium injection start timing and each rotation imaging timing by the imaging / imaging simulation unit of FIG. 8. FIG. 9 is a diagram illustrating an example of a timing chart and a list display of reduced DSA images for indicating an association between each rotation shooting timing and each reduced DSA image by the shooting imaging simulation unit of FIG. 8.

Hereinafter, an X-ray diagnostic apparatus according to the present invention will be described with reference to the drawings according to preferred embodiments.
(First embodiment)
As shown in FIG. 1, the X-ray diagnostic apparatus has an X-ray imaging mechanism 10. As shown in FIG. 2, the X-ray imaging mechanism 10 includes an X-ray tube 12 and an X-ray detector 14. The X-ray detector 14 is typically composed of a flat panel detector (FPD: planar X-ray detector) having semiconductor detection elements arranged in a matrix. The X-ray tube 12 together with the X-ray detector 14 is mounted on a substantially C-shaped arm 60 so as to face each other. The subject on the couch top 50 is disposed between the X-ray tube 12 and the detector 14. The image memory 25 is provided to store all the data (herein referred to as image data) output from the X-ray detector 14 and typically preprocessed.

  The C-arm 60 is supported by the rotation support mechanism 22 so as to be rotatable about three orthogonal axes XYZ. The rotation support mechanism 22 may be either a ceiling hanging type or a floor standing type. The rotation drive unit 23 is configured to individually rotate the C-arm 60 about each of the axes XYZ. When rotating, the C-arm 60 is rotated with the axis Z or the axis X as the rotation center axis.

  The X-ray diagnostic apparatus, together with the X-ray imaging mechanism 10, includes a rotation imaging controller 20, a detector controller 21, a rotation drive unit 23, an image memory 25, a subtraction unit 27, an affine transformation unit 32 that performs image enlargement movement, and the like. A configuration unit 34, a three-dimensional image processing unit 35, a D / A conversion unit 36, and a display unit 37 are included. The contrast medium injection device 24 may be a component of the X-ray diagnostic apparatus or may constitute an external device instead of a component.

  The rotational imaging controller 20 repeats rotational imaging a plurality of times after one (single) contrast agent injection, triggered by a contrast agent injection start signal output from the contrast agent injection device 24 at the start of contrast agent injection. Each of the plurality of rotational imaging operations is time-controlled and managed by a time (elapsed time) starting from a single contrast agent injection time. According to this, it becomes possible to perform a plurality of rotational imaging operations after one imaging, and it is possible to reduce the contrast burden on the subject that occurs when performing two or more imaging rotation imaging.

  The rotation imaging controller 20 controls the rotation drive unit 23 to rotate the C-arm 60 at high speed in rotation imaging, and controls the high voltage generation unit 26 during the rotation period to emit X-rays from the X-ray tube 12. The data is generated continuously or intermittently, and the detector controller 21 is controlled so that the X-ray detector 14 repeatedly executes data acquisition. Photographing is repeated in this rotational photographing, and the angular interval of the photographing is defined as a sampling pitch.

  FIG. 3 shows a typical rotational imaging sequence of the present embodiment. Here, a description will be given with an example of two rotation photographing. When the injection of the contrast agent into the subject is started from the contrast agent injection device 24, a signal indicating the start of the injection of the contrast agent is output from the contrast agent injection device 24. When the rotation controller 20 receives the signal, it sets the time as the starting point of the time management control.

  When the first time has elapsed from the contrast agent injection time, the rotation drive unit 23 rotates the C-arm 60 in the forward direction at a constant speed under the control of the rotary imaging controller 20. The rotation angle is set to 200 degrees, for example. At the same time, when the first time has elapsed from the injection time of the contrast agent, the high voltage generation unit 26 continuously or intermittently applies a high voltage (tube voltage) to the X-ray tube 12 under the control of the rotation imaging controller 20. Start application. Thereby, generation of X-rays is started from the X-ray tube 12 continuously or intermittently. The generated X-ray is shaped by the collimator device 16, passes through the subject, and is detected by the X-ray detector 14. The X-ray detector 14 repeats signal accumulation / signal readout in synchronization with X-ray generation and rotation of the C-arm 60 under the control of the detector controller 21 under the control of the rotation imaging controller 20. Thereby, image data is repeatedly output from the X-ray detector 14. In the first rotation shooting, the sampling pitch is set to 0.5 degrees, for example, and 400 frames of image data are acquired during the first rotation shooting period.

  After the first rotation shooting is completed, the C-arm 60 is rotated in the reverse direction and returned to the start position of the first rotation shooting.

  Next, when a second time longer than the first time elapses from the contrast agent injection time, the rotation driving unit 23 controls the C-arm 60 in the first direction in the forward direction under the control of the rotation imaging controller 20. Rotate at a constant speed at the same speed. The rotation angle is set to 200 degrees, which is the same as the first rotation shooting. At the same time, when the second time has elapsed from the injection time of the contrast agent, the high voltage generator 26 controls the X-ray tube 12 to perform high voltage continuous or first rotation imaging under the control of the rotation imaging controller 20. Start intermittent application at the same period. Thereby, generation of X-rays is started from the X-ray tube 12 continuously or intermittently at the same cycle as the first rotation imaging. The generated X-ray is shaped by the collimator device 16, passes through the subject, and is detected by the X-ray detector 14. In the X-ray detector 14, the control of the detector controller 21 under the control of the rotation imaging controller 20 synchronizes with the generation of X-rays and the rotation of the C-arm 60, and the signal accumulation / Repeat signal readout. Thereby, image data is repeatedly output from the X-ray detector 14. Even in the second rotation shooting, 400 frames of image data are acquired at the same sampling pitch of 0.5 degrees as in the first rotation shooting.

  In the second rotation imaging, the collimator opening of the collimator device 16 is narrowed down in the vertical direction so that only a specific region of interest is included in the field of view than that of the first rotation imaging, for example, as shown in FIG. Also good. Typically, in the first rotation imaging, the collimator opening covers the entire field of view FOV, and in the second rotation imaging, the collimator opening is narrowed down vertically in a specific region where hepatocellular carcinoma exists. The region of interest may be the immediately previous captured image, or the first captured image is used to determine the imaging range on the image with an input device (not shown) such as a mouse.

This completes the two rotation imaging performed after the injection of a single contrast agent.
In the first rotational imaging, CTHA (CT under hepatic arteriography) is typically used. In the second rotation photography, it is typically used to photograph a corona shadow around a hepatocellular carcinoma instead of the single level dynamic CTA.

In CTHA, a scattered radiation correction process is applied to a plurality of images (two-dimensional) collected by the first rotational imaging operation after contrast agent injection, and then a subtraction process is performed in the subtraction section from the image unevenness correction image. The beam hardening correction is performed in the hardening correction unit. A CTHA image (three-dimensional) is reconstructed by a three-dimensional reconstruction unit from the obtained plurality of corrected images (two-dimensional). Here, the image unevenness correction image is collected in a calibration operation once every several months, and is an image taken in a state where there is nothing between the X-ray tube and the detector.

  In the corona shadow photographing image, after performing scattered radiation correction, subtraction processing, and beam hardening processing in the same manner as described above for a plurality of images (two-dimensional) collected by the second rotational photographing operation after contrast agent injection, A three-dimensional reconstruction unit reconstructs a corona shadow image (three-dimensional).

  The three-dimensional image processing unit switches and displays the CTHA image and the corona shade image in a display mode such as an MPR image, a MIP (Maximum Intensity Projection) image, and a Volume Rendering image. In addition, the CTHA image and the corona shadow image are subtracted by the subtraction unit, and the subtraction image is combined with the CTHA image or the corona shadow image by changing the color so that the corona shadow exists around the hepatocellular carcinoma. Can be easily confirmed, and is useful information for the diagnosis of hepatocellular carcinoma.

  Thus, rotational imaging can be repeated a plurality of times after one (single) injection of a contrast agent, and the contrast burden on the subject can be reduced when performing two or more imaging rotational imaging.

  FIG. 5 shows a modification in the case where the subject to be imaged is a hepatic artery like CTHA. In this case, a rotation mask image having no contrast effect is collected before the start of contrast medium injection, and images of the hepatic artery are collected every time in the same manner as CTHA in the first rotation after the contrast medium injection, for a total of 200 frames, The second time, corona shadow images are collected every 0.5 degrees and a total of 400 frames are collected. The hepatic artery image is subtracted with the rotation mask image and then reconstructed by a three-dimensional reconstruction unit to obtain a three-dimensional hepatic artery image. Similar to the previous example, the corona shadow image is subjected to scattered ray correction, subtraction processing, and beam hardening processing, and then the three-dimensional reconstruction unit reconstructs the corona shadow image (three-dimensional). Since only blood vessel information can be extracted by subtraction with a mask image collected in advance, the target tumor can be depicted even if the number of projections is small. Therefore, this modification has an advantage that the amount of contrast medium injected into the patient can be reduced. The corona shadow is a faint shadow and requires a sufficient number of projections for reconstruction, but it hardly changes depending on the blood flow, so that it is not necessary to increase the amount of contrast medium for rendering.

  FIG. 6 shows another modification in the case where the subject to be imaged is the hepatic artery as in the case of CTHA. In this case as well, a rotating mask image without contrast effect is collected before the start of contrast medium injection, and images of the hepatic artery are collected every 0.5 degrees as in CTHA in the first rotational imaging after contrast medium injection. For 400 frames, the second time, vein images are collected every time, and a total of 200 frames are collected. As in the previous example, the hepatic artery image is subjected to scattered radiation correction, subtraction processing, and beam hardening processing, and a CTHA image (three-dimensional) is reconstructed by a three-dimensional reconstruction unit. The vein image is subtracted from the rotation mask image and then reconstructed by a three-dimensional reconstruction unit to obtain a three-dimensional vein image. Although the vein has a problem that the concentration of the contrast medium is thinned, only the blood vessel information can be extracted by subtraction with the mask image collected in advance, so that the vein can be depicted without particularly increasing the amount of the contrast medium. The sampling pitch for the first rotation shooting and the sampling pitch for the second rotation shooting may be set to be the same, or may be set differently depending on each shooting target and shooting mode. .

  Although not shown, the size of the columnar field of view FOV (usually handled by a radius) may be set to be the same for the first rotation shooting and the second rotation shooting. You may make it set and differ individually according to object and imaging | photography mode. When the field of view FOV is small, the X-ray tube 12 and the X-ray detector 14 may be shifted in the X-axis direction to ensure high resolution.

  As described above, in this embodiment, it is possible to reduce the contrast burden on the subject when performing contrast rotation imaging twice or more.

(Second Embodiment)
FIG. 7 shows a photographing procedure according to the second embodiment. FIG. 8 shows an apparatus configuration according to the second embodiment. The same parts as those in FIG. In this embodiment, application to a cerebral artery is typically considered.

  When the first time has elapsed from the contrast agent injection time, the rotation drive unit 23 rotates the C-arm 60 at a constant speed in the forward direction under the control of the rotation controller 20. In this first rotation imaging, the arterial portion having a high blood flow velocity is set as the region of interest, and therefore the rotation velocity is set to 50 degrees / sec, for example. The rotation angle is set to 200 degrees, for example. At the same time, when the first time has elapsed from the injection time of the contrast agent, the high voltage generation unit 26 continuously or intermittently applies a high voltage (tube voltage) to the X-ray tube 12 under the control of the rotation imaging controller 20. Start application. Thereby, generation of X-rays is started from the X-ray tube 12 continuously or intermittently.

  The generated X-ray is shaped by the collimator device 16, passes through the subject, and is detected by the X-ray detector 14. The X-ray detector 14 repeats signal accumulation / signal readout in synchronization with X-ray generation and rotation of the C-arm 60 under the control of the detector controller 21 under the control of the rotation imaging controller 20. Thereby, image data is repeatedly output from the X-ray detector 14. Since the arterial part does not require much density resolution, the sampling pitch is set to, for example, 2 degrees in consideration of the exposure dose, and 100 frames of image data are acquired during the first rotation imaging period.

  Next, when a second time longer than the first time elapses from the contrast agent injection time, the rotation drive unit 23 rotates the C-arm 60 in the reverse direction at a constant speed under the control of the rotation controller 20. In this second rotation imaging, unlike the imaging area of the first rotation imaging, the capillary blood vessel is set as a region of interest, and the rotation speed is the same as the rotation speed of the first rotation imaging to suppress the influence of veins. For example, it is set to the same, for example, 50 degrees / sec. The rotation angle is set to 200 degrees, for example. At the same time, when the second time has elapsed from the contrast agent injection time, the high voltage generator 26 continuously or intermittently applies a high voltage (tube voltage) to the X-ray tube 12 under the control of the rotary imaging controller 20. Start application. Thereby, generation of X-rays is started from the X-ray tube 12 continuously or intermittently. The generated X-ray is shaped by the collimator device 16, passes through the subject, and is detected by the X-ray detector 14.

  The X-ray detector 14 repeats signal accumulation / signal readout in synchronization with X-ray generation and rotation of the C-arm 60 under the control of the detector controller 21 under the control of the rotation imaging controller 20. Thereby, image data is repeatedly output from the X-ray detector 14. In the capillary vessel, the flow of the contrast agent is as fast as the arterial portion, but the density resolution requires a high level. Therefore, here, the frame rate is set to a frame rate faster than the frame rate of the first rotation imaging, and sampling is thereby performed. The pitch is set to 0.85 degrees, for example, and 250 frames of image data are acquired during the second rotation shooting period.

  Next, when a third time longer than the second time has elapsed from the contrast agent injection time, the rotation drive unit 23 rotates the C-arm 60 in the forward direction at a constant speed under the control of the rotation controller 20. In this third rotational imaging, unlike the imaging sites of the first and second rotational imaging, it is necessary to set both the capillary blood vessel and the vein as regions of interest and capture a finer density change. The speed is slower than the rotation speed of the first rotation shooting and the second rotation shooting, and is set to 30 degrees / sec, for example. The rotation angle is set to 200 degrees, for example. At the same time, when the third time has elapsed from the contrast agent injection time, the high voltage generator 26 continuously or intermittently applies a high voltage (tube voltage) to the X-ray tube 12 under the control of the rotary imaging controller 20. Start application. Thereby, generation of X-rays is started from the X-ray tube 12 continuously or intermittently. The generated X-ray is shaped by the collimator device 16, passes through the subject, and is detected by the X-ray detector 14. The X-ray detector 14 repeats signal accumulation / signal readout in synchronization with X-ray generation and rotation of the C-arm 60 under the control of the detector controller 21 under the control of the rotation imaging controller. Thereby, image data is repeatedly output from the X-ray detector 14. Since the density resolution in the capillaries and veins is required to be considerably high, the sampling pitch is set to 0.5 degrees, for example, and 400 frames of image data are acquired during the second rotation shooting period. Is done.

  In the arterial reconstruction, a plurality of images (two-dimensional) collected by the first rotational imaging operation after contrast agent injection are subtracted by the image (two-dimensional mask image) collected before the contrast agent injection and the subtraction unit 27 to obtain A three-dimensional reconstruction unit reconstructs an arterial image (three-dimensional) from the plurality of subtraction images (two-dimensional). In the case where a two-dimensional mask image is not collected, a scattered radiation correction process is applied by a scattered radiation correction unit to a plurality of images (two-dimensional) collected by the first rotational imaging operation after the injection of a contrast agent, and then image unevenness Subtraction processing is performed from the correction image by the subtraction unit, and beam hardening correction is performed by the beam hardening correction unit. The three-dimensional reconstruction unit reconstructs an Angio CT image (three-dimensional) from the obtained corrected images (two-dimensional).

  In the capillary blood vessel image, a plurality of images (two-dimensional) collected by the second rotational imaging operation after the contrast agent injection are subjected to scattered radiation correction, subtraction processing, and beam hardening processing in the same manner as described above. A capillary image (three-dimensional) is reconstructed by the dimension reconstruction unit. Capillary blood vessels generally have very thin contrast medium concentration information, and thus S / N deteriorates when reconstructed like an artery. In order to solve the problem, noise can be suppressed by changing the reconstruction filter and applying a filter that suppresses high frequency enhancement. The reconstruction is performed in the same manner as the artery, and the same effect can be obtained by applying a low-pass filter (low-pass filter) at the display stage.

  For capillary and venous images, after performing the scattered radiation correction, subtraction processing, and beam hardening processing on the plurality of images (two-dimensional) collected by the third rotational imaging operation after contrast agent injection, A three-dimensional reconstruction unit reconstructs a capillary / vein image (three-dimensional). Capillary vessel / venous images also have very thin contrast medium concentration information, and thus S / N deteriorates when reconstructed like an artery. In order to solve the problem, noise can be suppressed by changing the reconstruction filter and applying a filter that suppresses high frequency enhancement. In terms of the degree of high-frequency enhancement, high-frequency enhancement is the highest during arterial reconstruction, the next is the capillary / vein image reconstruction, and the closest to the low-pass filter is the reconstruction of the capillary image. The reconstruction is performed in the same manner as the artery, and the same effect can be obtained by applying a low-pass filter (low-pass filter) at the display stage.

  The three-dimensional image processing unit switches and displays the above-described arterial image, Angio CT image or capillary blood vessel image, capillary blood vessel / venous image in a display manner such as an MPR image, a MIP (Maximum Intensity Projection) image, and a Volume Rendering plane image. In addition, the arterial information extracted from the arterial image or the Angio CT image is synthesized and displayed in different colors from the capillary blood vessel image, capillary blood vessel / venous image, so that the blood flow of the artery and the nearby capillary blood vessel portion can be understood. Useful for. Furthermore, by subtracting the capillary / vein image and capillary image in the subtraction section, and displaying the subtraction image in a different color from the capillary image or capillary / vein image, the temporal density in the capillary section is displayed. The change can be roughly confirmed, and it becomes useful information about the suspicion of embolization and functional deterioration in the capillary blood vessel portion.

When performing multiple rotational imaging, especially as the time from contrast injection start time to each rotational imaging becomes longer, it becomes more susceptible to individual differences in blood flow velocity, and the conditions of each rotational imaging change, It is difficult to clarify the imaging procedure and determine the time from the contrast injection start time to the start of each rotation imaging. The apparatus according to the present embodiment is equipped with a shooting simulation unit 39 that supports setting of shooting procedures. The following description is a method for simplifying the setting procedure of the shooting procedure performed with the support of the shooting simulation unit 39.
1) Press the “Shooting sequence setting navigation” switch on the shooting program.
2) A large number of the previous captured images are displayed as reduced DSA images.

    3) A frame corresponding to the contrast start timing is identified. When the injection is performed using the automatic contrast medium injector, the timing at which the contrast start signal is sent to the automatic contrast medium injector is stored in association with the DSA image, and the timing is identified as the contrast start timing. When injecting with a syringe, the mouse selects a frame corresponding to the start of contrasting (left-click) and designates “select contrast start timing” from the pull-down menu to identify the contrast start timing. For example, here, (1, 3) (image 100 in the third row of the first row) in FIG. 9 is identified as an image collected at the contrast start timing.

    4) Identify the frame corresponding to the first time. A frame corresponding to the first time is identified by selecting (left-clicking) the frame corresponding to the first time and specifying “select the first rotation image capturing timing” from the pull-down menu. For example, here, (1, 5) in FIG. 9 (the image 101 in the fifth column of the first row) is identified as an image collected at the first rotation image capturing timing.

    5) Identify the frame corresponding to the second time. The frame corresponding to the second time is identified by selecting (left-clicking) the frame corresponding to the second time and specifying “select second rotation image capturing timing” from the pull-down menu. For example, here, (2, 5) in FIG. 9 (the image 102 in the second row and the fifth column) is identified as an image collected at the second rotation image capturing timing.

    6) Identify the frame corresponding to the third time. A frame corresponding to the third time is identified by selecting (left-clicking) the frame corresponding to the third time and specifying “select a third rotated image capturing timing” from the pull-down menu. For example, here, (5, 4) in FIG. 9 (the image 103 in the fourth column in the fifth row) is identified as an image collected at the third rotation image capturing timing.

    7) When all timings are identified, a timing chart is created by the imaging simulation unit 39 and displayed as illustrated in FIG. The time on the timing chart is associated with the reduced DSA image. Specifically, the portion corresponding to the first rotation shooting on the timing chart is displayed in red (the hatched portion in FIG. 10), and the image collected in the first rotation shooting is displayed surrounded by a red frame. The A portion corresponding to the second rotation shooting is displayed in blue (the left oblique line portion in FIG. 10), and an image collected in the second rotation shooting is displayed surrounded by a blue frame. A portion corresponding to the third rotation shooting is displayed in yellow-green (shaded portion in FIG. 10), and an image collected in the third rotation shooting is displayed surrounded by a yellow-green frame.

    8) When the operator instructs to display a moving image at this stage, all frames collected after the start of contrast medium injection are set as moving image display targets, and when an image collected by each rotational shooting is displayed during moving image reproduction. For example, information for distinguishing states such as “during first rotation shooting”, “during second rotation shooting”, and “during third rotation shooting” are displayed.

    9) Clicking on the part corresponding to the first rotation shooting on the timing chart, only the red frame surrounding the image collected in the first rotation shooting is clearly displayed and collected in the other second and third rotation shooting. A blue frame and a yellow-green frame surrounding the selected image are displayed in a mixed color with gray.

    10) When the operator instructs to display a moving image at this stage, an image collected by the first rotation shooting is set as a moving image display target, and only the image collected by the first rotation shooting is displayed as a moving image.

    11) When an arbitrary frame is clicked, the frame surrounding the image is emphasized, and the timing corresponding to the time is displayed by an arrow on the timing chart.

    12) The photographing start timing can be corrected on the timing chart and the reduced DSA image. Specifically, for example, while dragging the portion corresponding to the first rotation shooting (red frame), the left and right are moved. Alternatively, click on the frame to be changed on the reduced DSA image, and select the start of each shooting from the pull-down menu again.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  INDUSTRIAL APPLICABILITY The present invention can be applied to the field of providing an interface for reducing the burden of contrast on a subject when performing two or more contrast rotation imaging and accurately and easily identifying the imaging start time after the second imaging. There is.

  DESCRIPTION OF SYMBOLS 12 ... X-ray tube, 14 ... X-ray detector, 20 ... Rotation imaging controller, 21 ... Detector controller, 22 ... Rotation support mechanism, 23 ... Rotation drive part, 24 ... Contrast injection device, 25 ... Image memory, 26 ... high voltage generation unit, 27 ... subtraction unit, 32 ... affine transformation unit, 34 ... three-dimensional reconstruction unit, 35 ... three-dimensional image processing unit, 36 ... D / A conversion unit, 37 ... display unit, 60 ... C type arm.

Claims (18)

A substantially C-shaped arm;
A support mechanism for rotatably supporting the substantially C-shaped arm;
A rotation drive unit for driving rotation of the substantially C-arm;
An X-ray tube mounted on the substantially C-shaped arm;
A high voltage generator for generating a high voltage to generate X-rays from the X-ray tube;
An X-ray detector mounted on the substantially C-shaped arm in a direction facing the X-ray tube;
A plurality of rotational imaging operations, in which X-rays are continuously or intermittently generated from the X-ray tube while rotating the substantially C-shaped arm and X-ray detection is repeated by the X-ray detector, are performed after a single contrast medium injection. The operation of the support mechanism, the high voltage generator, and the X-ray detector is controlled in order to repeat the rotation, and each of the plurality of rotation imaging operations is started from the time of injection of the single contrast agent. An X-ray diagnostic apparatus comprising: a rotation imaging control unit that performs time control management according to the determined time. The X-ray diagnostic apparatus according to claim 1, further comprising an image reconstruction processing unit configured to reconstruct separately using a plurality of images collected by the rotational imaging operation. The X-ray diagnostic apparatus according to claim 2, wherein at least one of processing contents and processing parameters of the separate reconstruction processes is different. The second rotational imaging operation after the contrast medium injection by reconstructing an image by subtracting a plurality of images collected by the first rotational imaging operation after the contrast medium injection from the plurality of images collected before the contrast medium injection An image reconstruction processing unit that reconstructs an image using the plurality of images collected by
The rotation imaging control unit includes the support mechanism, the high voltage generation unit, and the X-ray detector so that a sampling pitch of the second rotation imaging operation is narrower than a sampling pitch of the first rotation imaging operation. The X-ray diagnostic apparatus according to claim 2, wherein: The rotation shooting control unit is configured to generate the high voltage so that a sampling pitch of at least one rotation shooting operation of the plurality of rotation shooting operations is narrower or wider than a sampling pitch of other rotation shooting operations. The X-ray diagnosis apparatus according to claim 1, wherein the X-ray diagnosis apparatus controls the X-ray detector and the X-ray detector. The X-ray diagnostic apparatus according to claim 2, wherein a spatial filter that emphasizes different spatial frequency bands is applied to the separately reconstructed images. In order to control the plurality of rotational shooting operations, further comprising an interface unit for setting the time,
The interface is
A display unit that displays a captured image collected in advance as a reference image;
A contrast start time identifying unit for identifying the contrast start time from the displayed captured image or its examination information;
The X-ray diagnostic apparatus according to claim 1, further comprising an imaging start time setting unit that sets the start times of the plurality of rotational imaging operations separately. A reference image identifying unit that identifies a captured image closest to the imaging start time as the reference image from the plurality of the previously collected captured images. The X-ray diagnostic apparatus according to claim 7, further comprising: The X-ray diagnostic apparatus according to claim 8, wherein the reference image identification unit changes the identified reference image to another captured image in accordance with an operator instruction. A shooting simulation unit configured to display a shooting start time set by the shooting start time setting unit and a shooting time determined based on shooting conditions determined by a shooting program in association with the reference image; The X-ray diagnostic apparatus according to claim 7. The X-ray diagnosis apparatus according to claim 10, wherein the imaging simulation unit displays images corresponding to imaging start times and imaging end times of a plurality of rotational imaging. The X-ray diagnosis apparatus according to claim 11, wherein the imaging simulation unit displays the image as a moving image together with the image. 13. The X according to claim 11, wherein the imaging simulation unit displays a part or all of a plurality of images collected by specific rotation imaging selected by an operator instruction. Line diagnostic equipment. The imaging simulation unit graphically displays a plurality of rotational imaging times starting from the contrast agent injection time as a time chart, and the rotational imaging period and the non-rotating imaging period are displayed in different colors on the display. The X-ray diagnostic apparatus according to claim 10, wherein display is performed. The X-ray diagnosis apparatus according to claim 14, wherein the imaging simulation unit displays the imaging time of the displayed image in association with the time chart. The X-ray diagnostic apparatus according to claim 1, wherein after the injection of the contrast agent, three rotation imaging operations with different sampling pitches are repeated. The apparatus further includes a variable collimator device that limits an X-ray irradiation field from the X-ray tube, and the X-ray irradiation field of at least one rotational imaging operation of the rotational imaging operation is more than the X-ray irradiation field of other rotational imaging operations. The X-ray diagnostic apparatus according to claim 1, wherein the collimator apparatus is controlled to be narrower or wider. The second rotational imaging operation after the contrast medium injection by reconstructing an image by subtracting a plurality of images collected by the first rotational imaging operation after the contrast medium injection from the plurality of images collected before the contrast medium injection The X-ray diagnostic apparatus according to claim 1, further comprising: an image reconstruction processing unit that reconstructs an image using the plurality of images collected as described above as they are.

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