JP2006110372A - X-ray diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an X-ray diagnostic apparatus which can make a rotation angle smaller than 180°. <P>SOLUTION: In the X-ray diagnostic apparatus which reconstructs 3-dimensional data of a subject from two or more X-ray projection images photographed from diverging photographing angles around the subject, 2 sets of photographing systems consisting of X-ray tubes 1 and 21, and X-ray detectors 2 and 22 are included, two or more X-ray projection images of diverging photographing angles within the limit from a 0 to a° are acquired by one photographing system, two or more X-ray projection images of diverging photographing angles within the limit from a to 2×a° are acquired by the other photographing system, and 3-dimensional data of the subject are reconstructed from two or more X-ray projection images of diverging photographing angles obtained by these 2 sets of photographing systems. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an X-ray diagnostic apparatus that reconstructs three-dimensional data of a subject.

  In this type of X-ray diagnostic apparatus, an X-ray tube and an image intensifier (II) that are opposed to each other with a subject sandwiched between them, as in X-ray computed tomography (X-ray CT), is a method of subject body axis. By repeating the imaging while rotating in the plane, X-ray projection images of a plurality of frames with different imaging angles are obtained, and the three-dimensional data of the subject is reconstructed from these X-ray projection images by back projection or logical sum. It is also called IICT. The problems that I.I.CT has are described below.

  A region indicated by a dotted line in FIG. 24A is a reconstruction region. This reconstruction area is defined as a sphere inscribed in a conical X-ray bundle for all directions. Imaging needs to be performed in a state where the subject P is accommodated in the reconstruction area. This can be understood by considering that the subject P is not accommodated in the reconstruction area. As shown in FIG. 24B, data of a part of the subject P indicated by the oblique lines protruding from the reconstruction area is captured from the b direction, but not from the a direction. Therefore, the data in the shaded area appears in the reconstructed image as an artifact. For this reason, I.I.CT required a large-diameter image intensifier. In addition, it was impossible to photograph a specific organ in the subject geometrically enlarged by bringing the X-ray tube close to the subject.

  In addition, since the X-ray tube and the image intensifier, which are large structures, are rotated at least 180 degrees, the rotation support mechanism is increased in size, and an imaging room with sufficient rotation space is required. There was a problem that it took a long time. Furthermore, at the time of angiographic imaging, it is necessary to take a so-called Max image before injecting the contrast agent, and there is a problem that the imaging time is prolonged.

  An object of the present invention is to provide an X-ray diagnostic apparatus capable of making the rotation angle smaller than 180 degrees.

  The present invention provides an X-ray diagnostic apparatus that reconstructs three-dimensional data of a subject from a plurality of X-ray projection images taken from different imaging angles around the subject, and includes at least an X-ray tube and an X-ray detector. Provided with two sets of imaging systems, one imaging system obtains a plurality of X-ray projection images with different imaging angles within a range from 0 degree to a degree, and the other imaging system obtains from a degree to 2 · a degrees A plurality of X-ray projection images having different imaging angles within a range are obtained, and three-dimensional data of the subject is reconstructed from the plurality of X-ray projection images having different imaging angles obtained by the two sets of imaging systems. To do.

  According to the present invention, the rotation angle can be made smaller than 180 degrees.

Preferred embodiments of the present invention will be described below with reference to the drawings.
(First embodiment)
FIG. 1 shows the configuration of the X-ray diagnostic apparatus according to the first embodiment. The X-ray tube 1 that irradiates the subject P with cone-beam X-rays and the image intensifier 2 that detects the X-rays transmitted through the subject P are kept facing each other with the subject P interposed therebetween. It is supported by a support mechanism (not shown) so as to be movable (rotatable) within the normal plane of the subject body axis. A TV camera 5 such as a CCD camera is mounted on the light output surface of the image intensifier 2 via an optical system. The high voltage generator 3 applies a tube voltage and a tube current to the X-ray tube 1 in a pulsed manner under the control of the X-ray controller 4.

  While the X-ray tube 1 and the image intensifier 2 rotate around the subject P, the imaging is repeated, and 72 frames of X-ray projection images with different imaging angles of, for example, 5 degrees are obtained. Note that a reconstruction area is defined as a sphere inscribed in a conical X-ray bundle with respect to all directions of the X-ray tube 1, and reconstruction is performed in the reconstruction area.

  The X-ray projection image signal is stored in the first image memory 7 using the imaging angle as an address before injection of the contrast medium via the analog-digital converter (A / D) 6, and after the injection of the contrast medium, the imaging is performed. The angle is stored in the second image memory 8 as an address. X-ray projection image data read out from the first image memory 7 and the second image memory 8 is sent to the subtraction processing means 9.

  The subtraction processing unit 9 subtracts (subtracts) two pieces of X-ray projection image data before and after the contrast agent injection having the same imaging angle. Thereby, 72 frames of subtraction image data having different shooting angles are created.

  The three-dimensional reconstruction means 10 reconstructs the three-dimensional data of the contrast agent part by applying an appropriate convolution filter to the 72 frames of subtraction image data and then performing back projection.

  The three-dimensional data is temporarily stored in the image memory 11. The display image creating means 12 creates display image data such as a surface image viewed from a viewpoint specified through an input device (not shown) using the three-dimensional data in the image memory 11. Display image data is converted into an analog signal by a digital-analog converter (D / A) 13 and then displayed on a monitor 14 such as a CRT display.

  Next, the operation of this embodiment will be described. 2 (a) shows the X-ray tube trajectory at the time of mask image photographing with a one-dot chain line, the solid line shows the X-ray tube trajectory at the time of contrast imaging, and FIG. 2 (b) contrasts the temporal change of the photographing angle. It is shown together with the agent injection timing. FIG. 3 shows a flow of image processing until three-dimensional data is reconstructed. In FIG. 2 (a), in order to distinguish the movement trajectory with both X-ray tubes, the alternate long and short dash line is not described with a solid line. However, in actuality, both X-ray tubes have the same circular trajectory. Rotate.

  First, in a state where the contrast agent is not injected into the subject P, the X-ray tube 1 and the image intensifier 2 make a round around the subject P between times t1 and t2 by the support mechanism. During this time, imaging is repeated, and 72 frames of X-ray projection images with different imaging angles, for example, 5 degrees, are obtained as mask images. These 72-frame mask image signals are stored in the first image memory 7 via the analog-digital converter 6 with each photographing angle as an address.

  Next, after the imaging of the mask image is completed, at time t3, the contrast medium is injected into the subject P by a doctor using an injector or by an automated injector. Between time t4 and t5 when the contrast agent is present in the region of interest, the X-ray tube 1 and the image intensifier 2 make a round around the subject P by the support mechanism. During this time, the imaging is repeated, and angiographic images of 72 frames with different imaging angles of, for example, 5 degrees are obtained as a live image. These 72 frames of live image signals are stored in the second image memory 8 via the analog-digital converter 6 with each shooting angle as an address.

  The mask image data and live image data read from the first image memory 7 and the second image memory 8 are sent to the subtraction processing means 9. The subtraction processing means 9 subtracts the two mask images and the live image before and after the contrast medium injection with the same imaging angle. Thereby, 72 frames of subtraction image data having different shooting angles are created. In this subtraction image, only the contrasted blood vessel shadow exists.

  These 72 frames of subtraction image data are subjected to an appropriate convolution filter by the three-dimensional reconstruction means 10 and then backprojected. Thereby, the three-dimensional data of only the blood vessel (contrast part) is reconstructed.

  This three-dimensional data is temporarily stored in the image memory 11. Display image data such as a surface image viewed from a viewpoint specified via an input device (not shown) is generated from the three-dimensional data in the image memory 11 by the display image generating means 12. Display image data is converted into an analog signal by the digital-analog converter 13 and then displayed on a monitor 14 such as a CRT display.

  As described above with reference to FIG. 24A, subtraction is performed between two images taken before and after contrast agent injection, and three-dimensional data of the contrast agent is reconstructed from the subtraction images. Data of a part of the subject P that protrudes from the reconstruction area is eliminated by subtraction, and thus artifacts are eliminated. Further, even when a part of the subject P protrudes from the reconstruction area, three-dimensional data free from artifacts can be obtained. Therefore, the X-ray tube is brought closer to the subject and the image intensifier is moved away from the subject. A specific organ (in this case, blood vessel) can be photographed in a geometrically enlarged manner.

(Second embodiment)
FIG. 4 shows the configuration of the X-ray diagnostic apparatus according to the second embodiment. Components identical with those shown in FIG. The second embodiment is characterized in that a partial image including a contrast agent shadow is extracted from an X-ray projection image for each imaging angle, and three-dimensional data of the contrast portion is reconstructed from these partial images. This will be specifically described below. Here, as in the first embodiment, it is assumed that 72 frames of max images with different shooting angles and 72 frames of live images with different shooting angles are obtained every 5 degrees.

  From the 72-frame max image and the live image, the subtraction processing unit 9 obtains a 72-frame subtraction image. The steps so far are the same as in the first embodiment. In the present embodiment, the concept of multi-stage slices (multi-slices) of X-ray CT is used, and reconstruction is performed for each slice plane. That is, a data row on one horizontal line of each X-ray projection image is treated as one-dimensional projection data (projection data) in terms of X-ray CT, and data of the same horizontal line number in the subtraction images at all imaging angles. A slice image of one slice plane is reconstructed from the row.

  The 72-frame subtraction image is taken into the slice dividing means 15 via the image memory 15. The slice dividing unit 15 attributes the horizontal line number and the shooting angle in units of horizontal lines for each subtraction image, and sends the attribute to the region limiting unit 17 as a one-dimensional data string.

  The area limiting unit 17 does not reconstruct a tomographic image for the horizontal line number (slice plane) when the data of 72 data strings having the same horizontal line number and different imaging angles indicate 0. In other words, the data string of the horizontal line number is not sent to the two-dimensional reconstruction unit 18 so as to be excluded from the reconstruction target. The shaded area in FIG. 5 indicates the removal area by the area limiting means 17. In addition, the area limiting unit 17 has a horizontal line number that is the same, and when data other than 0 is included in the data of 72 data strings having different imaging angles, the horizontal line number (slice plane) 72 data strings of the horizontal line number are sent to the two-dimensional reconstruction means 18 so as to reconstruct the image.

  Thus, by selecting data for each horizontal line, the region to be reconfigured is limited along the slice direction (subject body axis direction). Since the region of interest (contrast medium shadow, usually contrasted blood vessel) is imaged so as to be in the center of the image, the region of interest usually does not exist in several lines at the top and bottom of the image, and is zero level data. In each X-ray projection image, a portion excluding the upper and lower few lines is equivalent to a partial image including a contrast agent shadow.

  The two-dimensional reconstruction means 18 has the same horizontal line number sent from the area limiting means 17 and reconstructs a tomographic image from 72 data strings of all imaging angles here. This reconstruction is performed for all horizontal line numbers (slice planes) sent from the area limiting unit 17. Thereby, a plurality of tomographic images are reconstructed. A plurality of tomographic images created in this way are written in the three-dimensional image memory 11 with the horizontal line number as the attribute of the slice position. As a result, three-dimensional data is constructed in the three-dimensional image memory 11.

  As in the first embodiment, a display image is created by the display image creation 12 from the three-dimensional data written in the image memory 11 and displayed on the monitor 14 via the digital / analog converter 13.

  According to the second embodiment, since the reconstruction area can be limited, the reconstruction processing time can be shortened.

(Third embodiment)
FIG. 6 shows the configuration of the X-ray diagnostic apparatus of the third embodiment. The same parts as those in FIG. The X-ray diagnostic apparatus of the third embodiment includes a first imaging system comprising an X-ray tube 1, an image intensifier 2 and a TV camera 5, and an X-ray tube 21 having the same configuration as the first imaging system. Two imaging systems, ie, a second imaging system composed of an image intensifier 22 and a TV camera 25, are provided. As shown in FIG. 7B, the X-ray bundle center line from the X-ray tube 1 to the image intensifier 2 and the X-ray bundle center line from the X-ray tube 21 to the image intensifier 22 intersect at an angle α. Thus, both photographing systems are held by a rotation support mechanism (not shown). The smaller the angle α is, the more effective it is to shorten the photographing time. However, in order to avoid the interference of the large image intensifiers 2 and 22, the angle α is set to a specific angle within a range of 3 degrees to 45 degrees. When the rotation support mechanism rotates, the first imaging system rotates the circular orbit indicated by the solid line in FIG. 7A, and the second imaging system performs the first imaging as indicated by the alternate long and short dash line in FIG. The same orbit is rotated with a time delay of angle α from the system. A high voltage generator 23 is connected to the X-ray tube 21.

  The injector 27 is an automatic contrast medium injector, and the contrast medium is injected into the subject P via a syringe (injection cylinder) 29. The injector 27 injects the contrast agent while changing the instantaneous injection amount every moment so that the contrast agent concentration of the subject changes with time during the imaging period.

  The first imaging system repeats imaging while rotating around the subject P, and obtains 72 frames of X-ray projection images (referred to as first X-ray projection images) having different imaging angles, for example, by 5 degrees. These first X-ray projection images are sent to the first image memory 31 via the analog / digital converter 6 and stored therein. Similarly, the second imaging system repeats imaging while rotating around the subject P, and similarly to the first imaging system, 72 frames of X-ray projection images (second imaging angles different from each other by 5 degrees, for example) X-ray projection image). These second X-ray projection images are sent to the second image memory 32 via the analog / digital converter 26 and stored therein.

  The subtraction processing unit 9 subtracts the first X-ray projection image and the second X-ray projection image having the same imaging angle. Thereby, 72 frames of subtraction images with different shooting angles are created. After shooting at a shooting angle with the first shooting system, the second shooting system takes a shot at the same shooting angle after a delay time corresponding to the angle α and the angular velocity. Since the contrast medium concentration of the subject is changed with time by the injector 27, the contrast medium corresponding to the delay time is between the first X-ray projection image and the second X-ray projection image having the same imaging angle. There is a density difference. Therefore, by subtracting the first X-ray projection image and the second X-ray projection image having the same imaging angle, a contrast portion can be extracted according to this density difference.

  The 72-frame subtraction image created by the subtraction processing unit 9 is binarized by the binarization processing unit 30. The binarization processing unit 30 calculates the pixel average value of the subtraction image as a threshold value, and assigns 1 to pixels that are equal to or higher than the threshold value and 0 to pixels that are less than the threshold value. As a result, a binary image is obtained in which the contrast vessel portion has a pixel value of 1 and the other portions have a pixel value of 0.

  The binary image of 72 frames is temporarily stored in the image memory 33. The reconstruction unit 34 reconstructs the three-dimensional data of the contrasted blood vessel from the binary image of 72 frames by back projection and logical sum processing. This three-dimensional data is temporarily stored in the image memory 33. A display image created by the display image creation means 12 from the three-dimensional data is displayed on the monitor 14 via the digital / analog converter 13.

  Next, the operation of this embodiment will be described. FIG. 8 shows temporal changes in the imaging angles of the first and second imaging systems and temporal changes in the contrast agent injection amount. The first imaging system makes one rotation around the subject at an imaging angle of 0 to 360 degrees during a period from time t1 to t4. The second imaging system is rotated by a delay time Δt from the first imaging system and makes one rotation around the subject at an imaging angle of 0 to 360 degrees during a period from time t3 to t5. The contrast medium starts to be injected between time t1 and t3, that is, at time t2 between the time when the first imaging system passes through 0 degrees and the time when the second imaging system passes through 0 degrees, and the time elapses. As the instantaneous injection amount is gradually increased, the injection is continuously performed during the imaging period.

  The first imaging system repeats imaging at a constant cycle while rotating around the subject P at an imaging angle of 0 to 360 degrees. As a result, 72 frames of first X-ray projection images having different imaging angles of, for example, 5 degrees are obtained, and these first X-ray projection images are stored in the first image memory 31 via the analog-digital converter 6. Sent and memorized. Similarly, the second imaging system repeats imaging at a constant cycle while rotating around the subject P at an imaging angle of 0 ° to 360 °. As a result, 72 frames of second X-ray projection images having different imaging angles of 5 degrees, for example, are obtained, and these second X-ray projection images are stored in the second image memory 32 via the analog-digital converter 26. Sent and memorized.

  The first X-ray projection image and the second X-ray projection image are sent to the subtraction processing means 9. A first X-ray projection image and a second X-ray projection image having the same imaging angle are subtracted. Thereby, 72 frames of subtraction images with different shooting angles are created.

  For example, there is a time difference Δt from when the first imaging system performs imaging at an imaging angle of 180 degrees until the second imaging system performs imaging at the same imaging angle of 180 degrees. During this delay time Δt, the amount of contrast agent injected into the subject increases by ΔN, and the contrast agent concentration at the imaging region also increases accordingly. Therefore, by subtracting the first X-ray projection image and the second X-ray projection image having the same imaging angle, a contrast portion is extracted according to this density difference.

  The 72 frames of subtraction images created by the subtraction processing means 9 are each binarized by the binarization processing unit 30. The threshold for binarization is calculated by the binarization processing unit 30 as the pixel average value for each subtraction image. Pixels above this threshold are assigned 1 and pixels below the threshold are assigned 0, thereby obtaining a binary image having a contrast vessel portion having a pixel value of 1 and the other portions having a pixel value of 0.

  The binary image of 72 frames is temporarily stored in the image memory 33. The reconstruction means 34 reconstructs the three-dimensional data of the contrasted blood vessel from these 72-frame binary images by back projection and logical sum processing as shown in FIGS. 9A and 9B. This three-dimensional data is temporarily stored in the image memory 33. A display image created by the display image creation means 12 from the three-dimensional data is displayed on the monitor 14 via the digital / analog converter 13. Note that since binarization processing is included in this embodiment, contrast blood vessel density information cannot be obtained, but three-dimensional spatial information of contrast blood vessels can be obtained.

  As described above, in this embodiment, since it is not necessary to take a mask image, the photographing time can be shortened. Note that the three-dimensional reconstruction method for specifying the three-dimensional position of the contrast agent by back projecting the binarized subtraction image and taking the logical sum is to perform imaging while changing the contrast agent concentration. The subtraction image obtained by the X-ray imaging method described in the first embodiment may be binarized and the same processing may be performed. At this time, it is desirable that the pitch of the photographing angle is fine, but when there is only one target blood vessel, it is sufficient to obtain and reconstruct at least two images that do not face each other. In addition, when there are two or more target blood vessels or the target blood vessels are thick, it is necessary to use images in at least three directions that do not face each other.

(Fourth embodiment)
FIG. 10 shows the configuration of the main part of the X-ray diagnostic apparatus according to the fourth embodiment. The same parts as those in FIG. The X-ray diagnostic apparatus of the fourth embodiment is equipped with two imaging systems as in the third embodiment. As shown in FIG. 11B, the two imaging systems are held by a rotation support mechanism (not shown) so that the X-ray bundle center lines intersect each other at 90 degrees + β / 2. As shown in FIG. 13, when the spread angle of the X-ray bundles from the X-ray tubes 1 and 21 is α, β is preferably set so that β> α.

  The first X-ray projection image captured by the first imaging system before contrast is stored in the image memory 41. The first X-ray projection image imaged by the first imaging system after the contrast is stored in the image memory 42. The second X-ray projection image captured by the second imaging system before the contrast is stored in the image memory 43. The second X-ray projection image captured by the second imaging system after the contrast is stored in the image memory 44.

  The subtraction processing unit 45 performs subtraction between the two first X-ray projection images before and after the contrast with the same imaging angle. The subtraction processing means 46 performs subtraction between the two second X-ray projection images before and after the contrast with the same imaging angle. The subtraction images obtained by the subtraction processing means 45 and 46 are sent via the image memory 47 to a three-dimensional reconstruction means (not shown) as in the previous embodiment. Here, the three-dimensional data of the contrast vessel is reconstructed. A display image created from three-dimensional data by a display image creation means (not shown) is displayed on a monitor via a digital / analog converter.

  Next, the operation of this embodiment will be described. In FIG. 11A, the trajectories of the first and second imaging systems (here, X-ray tubes) at the time of mask image imaging are indicated by solid lines, and the first and second imaging systems (at the time of live image imaging after contrast imaging) ( Here, the trajectory of the X-ray tube is indicated by a one-dot chain line. In FIG. 12, the time change of the shooting angle of the first shooting system is indicated by a solid line, and the time change of the shooting angle of the second shooting system is indicated by a one-dot chain line.

  First, at the time of mask image photographing, the first and second photographing systems rotate 90 degrees + β / 2 clockwise from the initial photographing angles (0 degrees, 90 degrees + β / 2), respectively. As a result, the photographing angle of the first photographing system changes from 0 degree to 90 degrees + β / 2, and the photographing angle of the second photographing system changes from 90 degrees + β / 2 to 180 degrees + β. During this time t1 to t2, the first and second imaging systems are repeatedly imaged, and a plurality of first X-ray projection images and a plurality of second X-ray projection images are respectively captured as mask images. The first X-ray projection image as a mask image is stored in the image memory 41. The second X-ray projection image as a mask image is stored in the image memory 43.

  After time t2, a contrast agent is injected into the subject P at time t3. Then, the first and second imaging systems are each rotated by 90 ° + β / 2 clockwise from the imaging angle (90 ° + β / 2, 180 ° + β) at the end of mask image shooting, and each initial imaging angle. Return to. During this time t4 to t5, the first and second imaging systems are repeatedly imaged, and a plurality of first X-ray projection images and a plurality of second X-ray projection images are used as live images (angiographic images), respectively. Take a picture. The first X-ray projection image as a live image is stored in the image memory 42. The second X-ray projection image as a live image is stored in the image memory 44.

  Thus, by rotating by 90 degrees + β / 2, an X-ray projection image in a range of 0 degree to 90 degrees + β / 2 is obtained by the first imaging system, and 90 degrees + β / 2 is obtained by the second imaging system. An X-ray projection image in a range of ˜180 degrees + β is obtained. That is, an X-ray projection image in the range of 0 ° to 180 ° + β can be obtained by the two imaging systems, and therefore the rotation angle can be narrowed to shorten the imaging time.

  The post-contrast live images recorded in the image memories 42 and 44 are subtracted from the pre-contrast mask images in the image memories 41 and 43 taken from the same photographing angle. The image taken after the contrast medium injection recorded in the image memory 4 is subtracted from the image taken from the same angle and recorded in the image memory 3 before the contrast medium injection. A plurality of subtraction images in the range of 0 ° to 180 ° + β are sent to the three-dimensional reconstruction unit, and the three-dimensional reconstruction unit applies an appropriate convolution filter to the subtraction image, and then back-projects the subtraction images. Three-dimensional data of the contrast portion of the specimen is obtained. As for the three-dimensional data, a display image is created by a display image creating means. This display image is displayed on a monitor via a digital / analog converter.

(5th Example)
FIG. 14 shows the configuration of the main part of the X-ray diagnostic apparatus according to the fifth embodiment. The same parts as those in FIG. The X-ray diagnostic apparatus of the fifth embodiment is equipped with two imaging systems as in the third embodiment. As shown in FIG. 15B, the two imaging systems are held by a rotation support mechanism (not shown) so that the X-ray bundle center lines intersect at 90 degrees, that is, are orthogonal to each other. At the time of shooting, the two shooting systems rotate by an angle of 90 ° + β. During this time, shooting is repeated in each shooting system. Therefore, when the shooting angle is between 90 ° and 90 ° + β, shooting is performed at the same shooting angle in both shooting systems. As shown in FIG. 13, when the spread angle of the X-ray bundles from the X-ray tubes 1 and 21 is α, β is preferably set so that β> α.

  An X-ray projection image photographed at an imaging angle of 90 ° to 90 ° + β before contrast in each of the first and second imaging systems is sent to the comparison means 51. The comparison unit 51 compares the pixel values (pixel values of specific coordinates or pixel values total) of two X-ray projection images having the same imaging angle in the first and second imaging systems, and the sensitivity of both imaging systems. The first and second correction coefficients for the two photographing systems are calculated so as to be the same. A first X-ray projection image photographed before contrast enhancement by the first photographing system is sent from the image memory 41 to the correction means 52. The correcting unit 52 corrects the pixel value by multiplying each pixel of the first X-ray projection image by the first correction coefficient. The corrected first X-ray projection image is stored in the image memory 57 with the imaging angle as an attribute. Similarly, a second X-ray projection image photographed before contrast enhancement by the second photographing system is sent from the image memory 43 to the correcting means 53. The correcting unit 53 corrects the pixel value by multiplying each pixel of the second X-ray projection image by the second correction coefficient. The corrected second X-ray projection image is stored in the image memory 57 with the imaging angle as an attribute.

  The same is true after the contrast, and X-ray projection images photographed at a photographing angle of 90 ° to 90 ° + β after contrasting in each of the first and second photographing systems are sent to the comparison means 54. The comparison unit 54 compares the pixel values (pixel values of specific coordinates or pixel values total) of two X-ray projection images having the same imaging angle in the first and second imaging systems, and the sensitivity of both imaging systems. The third and fourth correction coefficients for the two photographing systems are calculated so that they are the same. A first X-ray projection image photographed after contrast enhancement in the first photographing system is sent from the image memory 42 to the correcting means 55. The correction unit 55 corrects the pixel value by multiplying each pixel of the first X-ray projection image by the third correction coefficient. The corrected first X-ray projection image is stored in the image memory 58 with the imaging angle as an attribute. Similarly, a second X-ray projection image photographed after contrast enhancement by the second photographing system is sent from the image memory 44 to the correction means 56. The correcting unit 56 corrects the pixel value by multiplying each pixel of the second X-ray projection image by the fourth correction coefficient. The corrected second X-ray projection image is stored in the image memory 58 with an imaging angle as an attribute.

  The subtraction processing means 59 reads X-ray projection images before and after contrast from the image memories 57 and 58. The subtraction processing unit 59 subtracts two X-ray projection images having the same imaging angle before and after contrast. The subtraction image obtained by the subtraction processing means 59 is sent to a three-dimensional reconstruction means (not shown) via the image memory 47 as in the previous embodiment. Here, the three-dimensional data of the contrast vessel is reconstructed. A display image created from three-dimensional data by a display image creation means (not shown) is displayed on a monitor via a digital / analog converter.

  Next, the operation of this embodiment will be described. FIG. 15A shows the trajectories of the first and second imaging systems (herein, X-ray tubes) at the time of mask image imaging by solid lines, and the first and second imaging systems (at the time of live image imaging after contrast imaging) ( Here, the trajectory of the X-ray tube is indicated by a one-dot chain line. In FIG. 16, the time change of the shooting angle of the first shooting system is indicated by a solid line, and the time change of the shooting angle of the second shooting system is indicated by an alternate long and short dash line.

  First, at the time of mask image photographing, the first and second photographing systems are rotated clockwise by 90 degrees + β from the initial photographing angles (0 degrees and 90 degrees), respectively. As a result, the shooting angle of the first shooting system changes from 0 degrees to 90 degrees + β, and the shooting angle of the second shooting system changes from 90 degrees to 180 degrees + β. During this time t1 to t2, the first and second imaging systems are repeatedly imaged, and a plurality of first X-ray projection images and a plurality of second X-ray projection images are respectively captured as mask images. The first X-ray projection image as a mask image is stored in the image memory 41. The second X-ray projection image as a mask image is stored in the image memory 43.

  After time t2, a contrast agent is injected into the subject P at time t3. Then, the first and second imaging systems rotate clockwise by 90 degrees + β from the imaging angles (90 degrees + β, 180 degrees + β) at the end of mask image capturing, respectively, and return to the initial imaging angles. During this time t4 to t5, the first and second imaging systems are repeatedly imaged, and a plurality of first X-ray projection images and a plurality of second X-ray projection images are used as live images (angiographic images), respectively. Take a picture. The first X-ray projection image as a live image is stored in the image memory 42. The second X-ray projection image as a live image is stored in the image memory 44.

  By rotating by 90 degrees + β in this way, an X-ray projection image in the range of 0 to 90 degrees + β is obtained by the first imaging system, and in the range of 90 to 180 degrees + β by the second imaging system. An X-ray projection image is obtained. That is, at the time of mask image shooting and live image shooting, X-ray projection images having the same shooting angle in both shooting systems can be obtained in the range of 90 ° to 90 ° + β.

  At least one mask image photographed at the same photographing angle in the photographing angle range of 90 ° to 90 ° + β is sent to the comparison unit 51 from the first and second photographing systems. The comparison means 51 compares the pixel values of the two mask images at the same shooting angle in the first and second imaging systems (pixel values of specific coordinates or pixel values in total), and the sensitivity of both imaging systems is The first and second correction coefficients for the two photographing systems are calculated so as to be the same. For example, a first correction coefficient 0.9 and a second correction coefficient 1.0 are calculated.

  The first mask image photographed before the contrast in the first photographing system is sent from the image memory 41 to the correcting means 52. The correction unit 52 corrects the pixel value by multiplying each pixel of the first mask image by the first correction coefficient. The corrected first mask image is stored in the image memory 57 with the shooting angle as an attribute. Similarly, a second mask image photographed before contrast enhancement by the second photographing system is sent from the image memory 43 to the correcting means 53. The correcting unit 53 corrects the pixel value by multiplying each pixel of the second mask image by the second correction coefficient. The corrected second mask image is stored in the image memory 57 with the shooting angle as an attribute.

  Similarly, live images taken at the same shooting angle in the range of 90 to 90 degrees + β are sent from the first and second shooting systems to the comparison unit 54 at least one by one. The comparison means 54 compares the pixel values of two live images at the same shooting angle in the first and second imaging systems (pixel values of specific coordinates or pixel values in total), and the sensitivity of both imaging systems is The third and fourth correction coefficients for the two photographing systems are calculated so as to be the same. For example, a third correction coefficient 0.9 and a fourth correction coefficient 1.0 are calculated.

  A first live image captured after contrast enhancement in the first imaging system is sent from the image memory 42 to the correction means 55. The correcting unit 55 corrects the pixel value by multiplying each pixel of the first live image by the third correction coefficient. The corrected first live image is stored in the image memory 58 with the shooting angle attributed. Similarly, a second live image captured after contrast enhancement by the second imaging system is sent from the image memory 44 to the correction unit 56. The correcting unit 56 corrects the pixel value by multiplying each pixel of the second live image by the fourth correction coefficient. The corrected second live image is stored in the image memory 58 with the shooting angle attributed.

  The post-contrast live image recorded in the image memory 57 is subtracted from the pre-contrast mask image of the image memory 58 taken from the same photographing angle. As a result, a plurality of subtraction images with shooting angles of 0 ° to 180 ° + β are created and stored in the image memory 47. A plurality of subtraction images are sent to the three-dimensional reconstruction unit, and the three-dimensional reconstruction unit applies an appropriate convolution filter to the subtraction image and then backprojects the three-dimensional data of the contrast portion of the subject. Is obtained. As for the three-dimensional data, a display image is created by a display image creating means. This display image is displayed on a monitor via a digital / analog converter.

  In this embodiment, the photographing time can be shortened as in the fourth embodiment, and the non-uniformity of sensitivity between the two photographing systems can be corrected.

(Sixth embodiment)
FIG. 17 shows the configuration of the X-ray diagnostic apparatus according to the sixth embodiment. The same parts as those in FIG. The X-ray diagnostic apparatus of the sixth embodiment has a configuration in which an image memory 60, a data correction unit 61, and an image memory 62 are added between the subtraction processing unit 9 and the three-dimensional reconstruction unit 10 in the configuration of FIG. is there. The data correction means 61 performs processing such as correcting the subtraction image manually, for example, removing unnecessary portions. For example, since the contrast medium is injected continuously for a relatively long time, the contrast medium may flow into the vein mainly in the latter half of the image. The purpose is to remove the contrasted vein portion.

  As shown in FIG. 18, the data correction means 61 designates an image memory 69 for temporarily recording the subtraction image and the corrected subtraction image, a display device 67 for displaying the subtraction image, and a removal portion to be removed from the subtraction image. The data input / output bus 68 is connected to the data / control bus 65, and the CPU 66 that removes the removal portion designated via the coordinate input device 68, that is, converts it to the same 0 value as the background.

  The image memory 60 stores subtraction images for all shooting angles. The subtraction images are sent one by one to the data correction means 61 and displayed on the display device 67. As shown in FIG. 19, the operator observes the display image, and designates a position where an unnecessary object is shown, for example, by a rectangular ROI via the coordinate input device 68. All the pixel values in the rectangular ROI are replaced with the same 0 value as the background. Such correction work is performed on the necessary subtraction images as shown in FIG. 20, and the corrected and uncorrected subtraction images are sent to the three-dimensional reconstruction means 10 via the image memory 62. The three-dimensional reconstruction means 10 obtains three-dimensional data of the contrast agent portion of the subject by applying a suitable convolution filter to the subtraction image and then performing back projection.

  In this way, unnecessary parts are removed in the previous stage of reconstruction, so that the reconstruction process can be saved, and the occurrence of artifacts due to the presence of contrast veins as described above in only some images can be prevented. . Further, this correction process can be performed by setting the subtraction image as a correction target. This is because an X-ray projection image (grayscale image) whose pixel value after correction is unknown cannot be corrected.

(Seventh embodiment)
FIG. 21 shows the configuration of the main part of the X-ray diagnostic apparatus according to the seventh embodiment. The same parts as those in FIG. In a reconstruction process, when a blood vessel portion captured at a certain imaging angle cannot be captured at another imaging angle, that is, when the subject partially protrudes from the reconstruction area, an artifact is generated in the reconstruction result. In the seventh embodiment, the occurrence of this type of artifact is prevented. The X-ray diagnostic apparatus of the seventh embodiment has the configuration shown in FIG. 17, the reconstruction area outside data determination means 72 between the image memory 60 and the data correction means 61, and the output of the reconstruction area outside data determination means 72. Further, a switch 73 for selectively connecting the data correcting means 61 and the image memory 62 is added.

  FIG. 22 is a flowchart showing the determination processing procedure of the reconstruction area outside data determination means 72. The outside reconstruction area data determination unit 72 takes in one subtraction image from the image memory 60 in step S1. In step S2, the peripheral area of this subtraction image is determined. Due to the input window of the image intensifier, a peripheral region having a width of one pixel indicated by hatching in FIG. 23 is determined for a circular subtraction image.

  Next, in step S3, a reference value for determining a pixel in which the subject (contrast blood vessel) is captured and a pixel in which the subject is not captured is determined. Since the determination target is a subtraction image, it is fixed to 0 value or 0 approximate value here. However, for example, an average value of all pixel values of the subtraction image may be calculated as a reference value. Next, in step S4, the peripheral pixels of the subtraction image are sequentially compared with the reference value.

  When all the peripheral pixels of the subtraction image are below the reference value, that is, when it is determined that all the images in the subtraction image are within the reconstruction area, the subtraction image is not corrected via the switch 73. Is sent to the image memory 62. On the other hand, when at least one peripheral pixel of the subtraction image exceeds the reference value, that is, when it is determined that an image outside the reconstruction area exists in the subtraction image, the subtraction image is transmitted via the switch 73 as data. It is sent to the correction means 61. That is, only the subtraction image for which it is determined that an image outside the reconstruction area exists is sent to the data correction unit 61, and the operator can be prompted to remove the image. Here, the removal of the blood vessel image to be removed as surrounded by the dotted line in FIG. 23 is manually performed by the data correction means 61.

  In this way, the image memory 62 holds a subtraction image of all angles in which no image outside the reconstruction area exists.

  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.

The block diagram of 1st Example. Operation | movement explanatory drawing of 1st Example. The process schematic diagram of 1st Example. The block diagram of 2nd Example. The figure which shows a removal area | region. The block diagram of 3rd Example. The figure which shows the rotation track | orbit of a 1st, 2nd imaging system. Operation | movement explanatory drawing of 3rd Example. The principle diagram of 3D reconstruction. The principal part block diagram of 4th Example. The figure which shows the rotation track | orbit of a 1st, 2nd imaging system. Operation | movement explanatory drawing of 4th Example. The figure which shows the divergence angle of a X-ray beam. The principal part block diagram of 5th Example. The figure which shows the rotation track | orbit of a 1st, 2nd imaging system. Operation | movement explanatory drawing of 5th Example. The block diagram of 6th Example. The block diagram of the data correction means of FIG. The conceptual diagram of data correction. Process outline | summary figure of 6th Example. The block diagram of the principal part of 7th Example. The flowchart which shows the process sequence of the data determination part outside a reconstruction area | region of FIG. The figure which shows a peripheral region. Explanatory drawing of one conventional problem.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 1 ... X-ray tube, 2 ... Image intensifier, 3 ... High voltage generator, 4 ... X-ray controller, 5 ... TV camera, 6 ... Analog-digital converter, 7, 8, 11 ... Image memory, 9 ... Subtraction processing means, 10... 3D reconstruction means, 12 ... Display image creation means, 13 ... Digital-analog converter, 14 ... Monitor.

Claims (4)

In an X-ray diagnostic apparatus for reconstructing three-dimensional data of a subject from a plurality of X-ray projection images taken from different imaging angles around the subject,
Provided with at least two sets of imaging systems consisting of an X-ray tube and an X-ray detector, with one imaging system obtaining a plurality of X-ray projection images with different imaging angles within a range from 0 degrees to a degrees, A plurality of X-ray projection images having different imaging angles within a range of a degree to 2 · a degrees are obtained by the imaging system, and the subject is obtained from the plurality of X-ray projection images having different imaging angles obtained by these two sets of imaging systems. An X-ray diagnostic apparatus characterized by reconstructing the three-dimensional data. In an X-ray diagnostic apparatus for reconstructing three-dimensional data of a subject from a plurality of X-ray projection images taken from different imaging angles around the subject,
Provided with at least two sets of imaging systems consisting of an X-ray tube and an X-ray detector, with one imaging system obtaining a plurality of X-ray projection images with different imaging angles within a range from 0 degrees to a degrees, A plurality of X-ray projection images having different imaging angles within a range from b degrees (b <a) to c degrees (c> a) are obtained by the imaging system, and two sets of imaging systems are obtained within a range from b degrees to a degrees. The difference in sensitivity between the two sets of imaging systems was obtained from the two X-ray projection images taken before the contrast agent injection at the same imaging angle, and the two sets of imaging systems were taken after the contrast agent injection based on this sensitivity difference. An X-ray diagnostic apparatus, wherein sensitivity of a plurality of X-ray projection images is corrected, and three-dimensional data of the subject is reconstructed from the plurality of X-ray projection images subjected to sensitivity correction. In an X-ray diagnostic apparatus for reconstructing three-dimensional data of a subject from a plurality of X-ray projection images taken from different imaging angles around the subject,
When β> α (α is the spread angle of the X-ray flux), two imaging systems consisting of an X-ray tube and an X-ray detector are provided so as to intersect at (90 + β / 2) degrees. A plurality of X-ray projection images having different imaging angles within a range from 0 degrees to (90 + β / 2) degrees are obtained by the system, and within a range from (90 + β / 2) degrees to (180 + β) degrees by the other imaging system. X-rays obtained by obtaining a plurality of X-ray projection images having different imaging angles and reconstructing three-dimensional data of a subject from the plurality of X-ray projection images having different imaging angles obtained by the two sets of imaging systems Diagnostic device. In an X-ray diagnostic apparatus for reconstructing three-dimensional data of a subject from a plurality of X-ray projection images taken from different imaging angles around the subject,
When β> α (α is the spread angle of the X-ray flux), two imaging systems composed of an X-ray tube and an X-ray detector are provided so as to intersect at 90 degrees, and one imaging system provides 0 degrees. A plurality of X-ray projection images having different imaging angles within a range from 1 to (90 + β) degrees, and a plurality of X-ray projection images having different imaging angles within a range from 90 degrees to (180 + β) degrees by the other imaging system. And obtain the difference in sensitivity between the two sets of imaging systems from the two X-ray projection images taken before the contrast agent injection at the same imaging angle in the two sets of imaging systems in the range from 90 degrees to (90 + β) degrees. Based on this sensitivity difference, sensitivity correction is performed on a plurality of X-ray projection images captured by two sets of imaging systems after injection of the contrast agent, and three-dimensional data of the subject is obtained from the plurality of sensitivity-corrected X-ray projection images. An X-ray diagnostic apparatus characterized by reconfiguration.

Images