JP2011172713A - Three-dimensional image display device and three-dimensional image display method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To ease a tired feeling of an observer by allowing the observer to easily recognize a side close to and a side far from the observer along the depth direction of a three-dimensional image thereby stabilizing the visual point of the observer. <P>SOLUTION: A three-dimensional image display device 22A includes: a right eye image display part 36 for displaying a right eye image 42r to be a two-dimensional image for the right eye 46r of the observer 20; a left eye image display part 34 for displaying a left eye image 42l to be a two-dimensional image for the left eye 46l of the observer 20; a three-dimensional image display part 40 for allowing the observe 20 to visually recognize the three-dimensional image based on the right eye image 42r and the left eye image 42l; and a display control part 160 causing a three-dimensional image display part 40 to display a marker image projected together with the three-dimensional image, on at least either the side close to or the side far from the observer along the depth direction of the three-dimensional image. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention provides a three-dimensional image display that allows the observer to visually recognize a three-dimensional image based on a two-dimensional image for the right eye of the observer (right eye image) and a two-dimensional image for the left eye of the observer (left eye image). The present invention relates to an apparatus and a three-dimensional image display method.

  Conventionally, a two-dimensional image (right-eye image) for the right eye of the observer is displayed on the right-eye image display unit, and a two-dimensional image (left-eye image) for the left eye of the observer is displayed on the left-eye image display unit, A three-dimensional image display in which the right-eye image and the left-eye image can be visually recognized as a three-dimensional image by an observer viewing the right-eye image and the left-eye image through a three-dimensional image display unit such as stereoscopic glasses. The device is known.

  In addition, patent documents 1-8 are disclosed as a prior art regarding visual recognition of the three-dimensional image by an observer.

JP 2008-178662 A JP 2006-230906 A Patent No. 4176504 JP 2003-245289 A JP 2004-73349 A JP 2004-271604 A JP 2007-75630 A JP 2003-24321 A

  By the way, when a viewer visually recognizes a three-dimensional image through the three-dimensional image display unit, it may be difficult to visually determine the near side or the deep side of the three-dimensional image along the depth direction of the three-dimensional image. Thus, if the near side and the back side of the three-dimensional image cannot be grasped, the depth range of the three-dimensional image cannot be recognized. As a result, the observer's viewpoint is not stable (is not determined), and there is a possibility that the observer's feeling of fatigue increases.

  However, although Patent Documents 1 to 4 propose that a marker is superimposed and displayed on a two-dimensional image or a three-dimensional image, the marker is intended to reduce the stability of the observer's viewpoint and fatigue. Therefore, even if the techniques of Patent Documents 1 to 4 are applied to a three-dimensional image display device, the above problem cannot be solved. Patent Documents 5 to 8 propose techniques related to three-dimensional image display, but none are techniques for solving the above problems.

  The present invention has been made in view of the above problems, and by stabilizing the viewpoint of the observer by making it possible to easily grasp the near side and the far side along the depth direction of the three-dimensional image, An object of the present invention is to provide a three-dimensional image display device and a three-dimensional image display method for reducing fatigue of the observer.

  A three-dimensional image display device according to the present invention displays a right-eye image display unit that displays a right-eye image that is a two-dimensional image for the right eye of the observer, and a left-eye image that is a two-dimensional image for the left eye of the observer. A left-eye image display unit, a three-dimensional image display unit that allows the observer to visually recognize a three-dimensional image based on the right-eye image and the left-eye image, and the near side and the back side along the depth direction of the three-dimensional image, At least one has a display control unit that displays a marker image captured together with the three-dimensional image on the three-dimensional image display unit.

  Further, the 3D image display method according to the present invention displays a right eye image, which is a 2D image for the right eye of the observer, on the right eye image display unit, and a left eye image, which is a 2D image for the left eye of the observer. Is displayed on the left-eye image display unit, and when the viewer visually recognizes the three-dimensional image based on the right-eye image and the left-eye image by the three-dimensional image display unit, the front side along the depth direction of the three-dimensional image A marker image taken together with the three-dimensional image is displayed on the three-dimensional image display unit on at least one of the side and the back side.

  According to these inventions, at least one of the near side and the back side along the depth direction of the three-dimensional image is displayed with the marker image taken together with the three-dimensional image.

  Accordingly, the observer can clearly recognize the depth range of the three-dimensional image by visually recognizing the marker image, and the space of the three-dimensional image can be easily grasped. That is, the observer can easily grasp the front side and the back side of the three-dimensional image by using the marker image as a support when stably viewing the three-dimensional image. It becomes possible to clearly recognize the depth range of the three-dimensional image. As a result, when visually recognizing the three-dimensional image, the observer's line of sight is stabilized and the fatigue of the observer can be reduced.

  Therefore, according to the present invention, it is possible to easily grasp the near side and the far side along the depth direction of the three-dimensional image by displaying the marker image on the near side or the far side of the three-dimensional image. In addition, it is possible to stabilize the observer's viewpoint and reduce the fatigue of the observer.

  In this case, it is easy to stabilize the observer's line of sight and reduce fatigue by displaying the marker image on at least one of the foremost part and the innermost part along the depth direction of the three-dimensional image. Can be realized.

  Further, when noise is present in the right-eye image or the left-eye image, since the viewing angles are usually not uniform, the noise is not stereoscopically viewed. However, although there is a slight amount, there is a case where there is a noise that is a stereoscopic view. In this case, the noise is also generated on the stereoscopic image (three-dimensional image). In the diagnostic interpretation, small points are also diagnosed, so it is desirable that the noise can be reduced as much as possible. In the present invention, if such noise is a location deeper (back side) than the innermost portion where the marker image is displayed, or a location shallower (front side) than the frontmost portion, the noise Can be removed.

  Further, if the marker images are respectively displayed on both the near side and the far side along the depth direction of the 3D image, the observer can view the 3D image when viewing the 3D image. On the other hand, since it becomes easy to feel a volume feeling (depth feeling), it is possible to further stabilize the observer's line of sight and further reduce fatigue.

  Further, the display control unit displays the right eye image and the right eye marker image on the right eye image display unit, and displays the left eye image and the left eye marker image on the left eye image display unit, whereby the three-dimensional image is displayed. The three-dimensional image, the right eye marker image, and the left eye marker image may be displayed together on the display unit.

  As a result, two marker images (the right eye marker image and the left eye marker image) are displayed on the near side and / or the back side along the depth direction of the 3D image, so that the depth of the 3D image is displayed. The range can be easily recognized.

  Here, the radiation detector detects the radiation transmitted through the subject when the radiation source irradiates the radiation detector through the subject from one angle with respect to the radiation detector. The left-eye image is transmitted through the subject when the radiation source irradiates the radiation detector through the subject from the other angle with respect to the radiation detector. The other radiation image acquired by the radiation detector detecting the radiation may be used.

  In this case, when a marker is arranged in at least one of the radiation source and the subject and between the subject and the radiation detector, the right eye marker image is the one of the ones. When the radiation source irradiates the subject and the marker with the radiation from an angle, the image of the marker is reflected in the one radiation image, and the left eye marker image is the radiation source from the other angle. Is an image of the marker that appears in the other radiation image when the subject and the marker are irradiated with the radiation.

  Thus, the marker is arranged between the radiation source and the subject or between the subject and the radiation detector, and the image of the marker is applied to the right-eye marker image and the The right eye marker image and the left eye marker image can be easily obtained by imprinting each radiographic image obtained by the above-described stereo imaging as a left eye marker image.

  When the observer (doctor) interprets and interprets the radiographic images obtained by such stereo imaging, and the three-dimensional image based on the radiographic images, image diagnosis is performed in the following order: The following remarkable effects can be obtained.

  First, the doctor diagnoses each radiographic image by interpretation. In this case, the right eye marker image or the left eye marker image is displayed in each of the radiation images. Therefore, after that, even when the three-dimensional image is displayed and both the right-eye marker image and the left-eye marker image are displayed, the doctor uses the right-eye marker image and the left-eye marker image as clues. Thus, it is possible to perform interpretation diagnosis on the three-dimensional image.

  Next, the doctor interprets and interprets the three-dimensional image based on each radiation image. In this case, since the right-eye marker image and the left-eye marker image are both displayed in the three-dimensional image, the depth range of the subject (imaging region) reflected in the three-dimensional image can be easily recognized. In addition, the right eye marker image and the left eye marker image provide support for stabilizing the viewpoint of the doctor during the interpretation diagnosis. As a result, the doctor's line-of-sight stability and fatigue can be reduced during the interpretation diagnosis, so that the diagnostic performance for the three-dimensional image can be improved.

  The radiation detector is housed in an imaging table that holds the breast of the subject, and the breast is compressed by a compression plate that is displaced from the radiation source side toward the imaging table and the imaging table, The marker is provided on at least one of the compression plate and the breast side of the imaging table and the radiation detector, and the breast is compressed and held by the compression plate and the imaging table. In the state, the radiation is irradiated from the radiation source to the radiation detector through the breast.

  Even in the diagnostic interpretation of a three-dimensional image based on each radiation image of the breast, the right eye marker image and the left eye marker image are reflected in the three-dimensional image, so that the diagnostic performance for the breast is improved. be able to.

  The radiation detector may be housed in a photographing table facing the subject, and the marker may be disposed on at least one of the radiation source side and the photographing table side of the subject.

  When each radiographic image is acquired by stereo imaging in such general imaging (for example, imaging of the subject's chest), even if interpretation diagnosis is performed on a three-dimensional image based on these radiographic images, the 3 Since the right-eye marker image and the left-eye marker image are reflected in the three-dimensional image, the diagnostic performance for the subject can be improved.

  Further, if the marker has a shape different from that of the subject and can absorb the radiation, the image of the subject and the marker image for the right eye are used when the doctor performs an interpretation diagnosis on the three-dimensional image. And the left eye marker image can be easily distinguished.

  In the above description, the marker is arranged in the vicinity of the subject, and the radiation image, the right-eye marker image, and the left-eye marker image are obtained by irradiating the subject and the marker with the radiation. there were.

  The present invention is not limited to the above description, and the right eye marker image and the left eye marker image based on a virtual marker can be displayed together with the three-dimensional image.

  That is, the three-dimensional image display device is configured to detect the right eye marker image based on the thickness of the subject, the one angle, the other angle, and the distance between the radiation source and the radiation detector. The display control unit further includes a shift amount calculation unit that calculates a shift amount with respect to the left eye marker image, and the display control unit displays the right eye marker image on the right eye image display unit based on the shift amount, and The left eye marker image is displayed on the left eye image display unit.

  Even in this case, since the right-eye marker image and the left-eye marker image based on the shift amount are displayed together in the three-dimensional image, the doctor efficiently performs an interpretation diagnosis on the three-dimensional image. It becomes possible.

  Further, the shift amount calculation unit calculates a minimum shift amount when the right eye marker image and the left eye marker image are displayed on the foremost portion along the depth direction, and / or the right eye marker. A maximum shift amount when the image and the left-eye marker image are displayed in the innermost portion along the depth direction is calculated.

  Thereby, the right eye marker image and the left eye marker image based on the minimum deviation amount are displayed in the foremost part, and the right eye marker image based on the maximum deviation amount and the right eye marker image are displayed in the innermost part. Since the left-eye marker image is displayed, the doctor can easily feel a volume feeling (depth feeling) with respect to the three-dimensional image when viewing the three-dimensional image. As a result, it is possible to easily stabilize the line of sight of the doctor and reduce fatigue, and further improve the diagnostic performance for the three-dimensional image.

  The three-dimensional image display device instructs the display control unit whether to display the right-eye marker image on the right-eye image display unit and whether to display the left-eye marker image on the left-eye image display unit. You may further have a display instruction | indication part to do.

  Further, the display control unit can change the shape and / or size of the right eye marker image and the left eye marker image based on the shape and / or size of the right eye image and the left eye image. Also good.

  Furthermore, the display control unit can change the display positions of the right eye marker image and the left eye marker image along the depth direction based on the shape and / or size of the right eye image and the left eye image. It may be.

  By adding these functions to the three-dimensional image display device, it is possible to perform an interpretation diagnosis by the doctor more efficiently.

  According to the present invention, by displaying the marker image on the near side or the far side of the three-dimensional image, the near side and the far side along the depth direction of the three-dimensional image can be easily grasped and observed. It is possible to stabilize the observer's viewpoint and reduce the fatigue of the observer.

1 is a block diagram of a schematic configuration of a radiographic image capturing system including a three-dimensional image display device according to a first embodiment. It is a perspective view of the mammography apparatus which comprises the radiographic imaging system of FIG. It is a partial side view of the mammography apparatus of FIG. It is a front view which shows stereo imaging | photography. It is a perspective view of the three-dimensional image display apparatus of FIG. It is a side view of the three-dimensional image display apparatus of FIG. 7A is an explanatory diagram of a right eye image, FIG. 7B is an explanatory diagram of a left eye image, and FIG. 7C is an explanatory diagram of a three-dimensional image (3D image). FIG. 2 is a block diagram illustrating the configuration of the radiographic image capturing system in FIG. 1 in more detail. It is a flowchart which shows operation | movement of the radiographic imaging system of FIG.1 and FIG.8. 10A and 10B are explanatory diagrams of other 3D images. FIG. 11A is a side view showing general photographing, and FIG. 11B is a plan view showing stereo photographing in general photographing. 12A is an explanatory diagram of a right eye image, FIG. 12B is an explanatory diagram of a left eye image, and FIG. 12C is an explanatory diagram of a 3D image. It is a block diagram of the radiographic imaging system provided with the three-dimensional image display apparatus which concerns on 2nd Embodiment. It is a front view which shows the stereo imaging | photography in the radiographic imaging system of FIG. It is a flowchart which shows a partial operation | movement of the radiographic imaging system of FIG.

  A preferred embodiment of the three-dimensional image display apparatus according to the present invention will be described with reference to FIGS. 1 to 15 in relation to the three-dimensional image display method.

  First, a radiographic imaging system 10A incorporating a three-dimensional image display device 22A according to the first embodiment will be described with reference to FIGS.

  As schematically shown in FIG. 1, the radiographic imaging system 10A basically performs stereo imaging to irradiate the radiation 16b and 16c from two different angles with respect to the mammo (breast) 14 of the subject 12. Thus, one of the two radiographic images acquired by the mammography apparatus (radiographic image capturing apparatus) 18A for acquiring the two radiographic images captured by the mammo 14 and the mammography apparatus 18A is obtained as a doctor or an engineer. And so on, and the other radiation image is a two-dimensional image (left-eye image 42l) for the left eye 46l of the observer 20, so that the right-eye image is obtained. The three-dimensional image display device 22A is configured to make the observer 20 visually recognize a three-dimensional image based on the 42r and the left-eye image 42l.

  In this case, the mammography apparatus 18A has the B position rotated by an angle of + θ1 with respect to the A position (θ = 0 °) on the central axis 24 passing through the approximate center of the mammo 14, or C rotated by an angle of −θ1. A radiation source 26 for irradiating the mammo 14 with radiation 16b and 16c from the position, and a solid state detector (radiation) for detecting the radiation 16b and 16c transmitted through the mammo 14 and converting them into radiation images (right eye image 42r and left eye image 42l). Detector 28, housing solid detector 28, and holding table 30 for holding mammo 14, and displacing mammo 14 together with shooting table 30 by moving toward radiation table 26 from radiation source 26 side. And a compression plate 32 to be held.

  In FIG. 1, the right eye image 42r is obtained by irradiating the mammo 14 with the radiation 16b from the radiation source 26 arranged at the position B, and detecting the radiation 16b transmitted through the mammo 14 with the solid state detector 28. On the other hand, the left eye image 42l is obtained by irradiating the mammo 14 with the radiation 16c from the radiation source 26 arranged at the position C and detecting the radiation 16c transmitted through the mammo 14 with the solid state detector 28. The case is illustrated. The central axis 24 is a vertical axis that passes through the approximate center of the mammo 14 and is substantially orthogonal to the upper surface of the imaging table 30 and the solid state detector 28.

  The three-dimensional image display device 22A includes a left eye image display unit 34 that displays a left eye image 42l, a right eye image display unit that is disposed at a position rotated by a predetermined angle with respect to the left eye image display unit 34, and displays a right eye image 42r. 36 and the left eye image display unit 34 which is disposed at a predetermined position between the left eye image display unit 34 and the right eye image display unit 36 and transmits the display light 44l of the left eye image 42l displayed by the left eye image display unit 34 to the viewer 20 side. A half mirror 38 that outputs and reflects the display light 44 r of the right eye image 42 r displayed by the right eye image display unit 36 toward the viewer 20, and stereoscopic glasses (three-dimensional image display unit worn by the viewer 20). 40).

  In this case, the observer 20 views the right eye image 42r indicated by the display light 44r from the half mirror 38 with the right eye 46r via the stereoscopic glasses 40, and the left eye image 42l indicated by the display light 44l from the half mirror 38. Can be visually recognized as a three-dimensional image (3D image) by viewing the right eye image 42r and the left eye image 42l (the synthesized image thereof).

  Next, a specific configuration of the mammography apparatus 18A will be described with reference to FIGS.

  The mammography apparatus 18A basically includes a base 50 that is installed in an upright state, and an arm member 54 that is fixed to a distal end portion of a turning shaft 52 that is disposed at a substantially central portion of the base 50. The radiation source accommodating portion 56 that accommodates the radiation source 26 and is fixed to one end of the arm member 54, the imaging table 30 that is fixed to the other end of the arm member 54, the radiation source accommodating portion 56 and the imaging table 30. And a compression plate 32 provided therebetween. The base 50 is provided with a display operation unit 64 that displays imaging conditions such as an imaging region of the subject 12, ID information of the subject 12, and the like, and can set such information as necessary.

  The arm member 54 that couples the radiation source storage unit 56 and the imaging stand 30 is configured to be rotatable about the turning shaft 52 so that the direction of the subject 12 relative to the mammo 14 can be adjusted. In addition, the radiation source accommodating portion 56 is connected to the arm member 54 via a hinge portion 58, and is configured to be rotatable independently from the imaging table 30 in the direction of the arrow θ.

  The arm member 54 is provided with a groove 60 along the arrow Z direction on the side (front side) opposite to the subject 12, while the handle for the subject 12 to hold on both sides in the arrow Y direction. The parts 62r and 62l are provided, respectively. The compression plate 32 is disposed between the radiation source accommodating portion 56 and the imaging table 30 by inserting the base end portion of the compression plate 32 into the groove portion 60 and fitting with the attachment portion (not shown). By displacing along the groove portion 60 in the arrow Z direction, it can be displaced in the arrow Z direction integrally with the mounting portion.

  In addition, in the irradiation range (irradiation field) of the radiations 16b and 16c below the compression plate 32, the radiations 16b and 16c can be absorbed and a marker 70 having a shape clearly different from that of the mammo 14 is provided. . Further, the radiation 16b, 16c can be absorbed within the irradiation range of the radiation 16b, 16c between the upper surface of the imaging table 30 and the solid state detector 28, and the shape of the mammo 14 and the marker 70 is clearly different. A marker 72 is provided.

  As such markers 70 and 72, for example, spheres, frames, rings, and metal pieces made of metal capable of absorbing the radiation 16b and 16c are employed. Also, it is desirable that the shapes of the markers 70 and 72 are different from each other at a glance. For example, one marker may be triangular and the other marker may be spherical in plan view.

  Further, in FIGS. 2 to 4, as an example, a case where one marker 70 is disposed below the compression plate 32 and the other marker 72 is disposed on the imaging table 30 is illustrated. There is no limit. That is, one marker 70 is provided at an arbitrary position within the irradiation range of the radiations 16 b and 16 c between the mammo 14 and the radiation source 26, and the other marker 72 is provided between the mammo 14 and the solid state detector 28. What is necessary is just to be provided in the arbitrary positions within the irradiation range of the radiation 16b and 16c in between. That is, the marker 72 is arranged on the front side (solid detector 28 side) of the mammo 14 along the arrow Z direction with respect to the solid detector 28, and the marker 70 is located behind the mammo 14 along the arrow Z direction. More preferably, the marker 72 is arranged on the foremost part of the mammo 14 (upper surface of the imaging table 30) along the arrow Z direction with respect to the solid state detector 28. The marker 70 may be provided at the innermost part of the mammo 14 along the arrow Z direction (the bottom surface of the compression plate 32).

  Therefore, as shown in FIG. 4, when the radiation 16b is irradiated to the mammo 14 from the radiation source 26 arranged at the B position, the radiation 74b irradiated to the marker 70 out of the radiation 16b is As a result, the projected image of the marker 70 appears in the right eye image 42r as a marker image 76b (see FIG. 7A). Of the radiation 16b, the radiation 78b applied to the marker 72 is absorbed by the marker 72. As a result, the projected image of the marker 72 appears in the right-eye image 42r as a marker image 80b.

  On the other hand, when the radiation 16c is irradiated to the mammo 14 from the radiation source 26 arranged at the position C, the radiation 74c irradiated to the marker 70 out of the radiation 16c is absorbed by the marker 70, and as a result. The projected image of the marker 70 appears in the left eye image 42l as a marker image 76c. Of the radiation 16c, the radiation 78c applied to the marker 72 is absorbed by the marker 72. As a result, the projected image of the marker 72 appears in the left eye image 42l as a marker image 80c.

  Since the right eye image 42r and the left eye image 42l are respectively acquired by the same solid state detector 28, the deviation amount between the marker image 76b reflected in the right eye image 42r and the marker image 76c reflected in the left eye image 42l is calculated. If Δl1 ′ is set, and the amount of deviation between the marker image 80b reflected in the right-eye image 42r and the marker image 80c reflected in the left-eye image 42l is Δl2 ′, the marker 72 is relative to the solid state detector 28. Since the marker 70 is disposed at a close position, and on the other hand, the marker 70 is disposed at a relatively far position, a relationship of Δl1 ′> Δl2 ′ is established between these deviation amounts (see FIG. 4).

  2 to 4 illustrate the case where the two markers 70 and 72 are provided on the mammography apparatus 18A, the first embodiment is not limited to the above-described configuration. Of the two markers 70 and 72, at least one marker may be disposed on the mammography apparatus 18A.

  Next, a specific configuration of the three-dimensional image display device 22A will be described with reference to FIGS.

  The three-dimensional image display device 22A includes a base 102 disposed on the upper surface of the desk 100, a support member 104 extending upward from the base 102, and a liquid crystal display supported in an upright state by the support member 104. A left-eye image display unit 34, a support member 106 that is curved and extends upward from the rear side of the left-eye image display unit 34, and a liquid crystal display that is supported in an inclined state with respect to the left-eye image display unit 34 by the support member 106 And a right-eye image display unit 36 and a half-mirror support mechanism 107 that is supported by the support member 106 and extends into a space between the upper surface of the desk 100 and the right-eye image display unit 36 in front of the left-eye image display unit 34. A half mirror 38 supported at a predetermined position between the left eye image display unit 34 and the right eye image display unit 36 by the half mirror support mechanism 107, and the observer 20 An operation unit 116 such as a keyboard to be operated, and a stereoscopic glasses 40 that the observer 20 is mounted.

  The half mirror support mechanism 107 is supported by a cylindrical shaft portion 108 penetrating the support member 106 in the horizontal direction, and both ends of the shaft portion 108, and the left eye image display unit 34 and the right eye are centered on the shaft portion 108. A substantially U-shaped rotating member 112 that can rotate between the image display unit 36 and a frame member 114 that is connected to the rotating member 112 and supports the peripheral portion of the half mirror 38.

  The rotating member 112, the frame member 114, and the half mirror 38 are restricted from rotating about the shaft portion 108 by the observer 20 turning the handle 110 to displace the handle 110 toward the shaft portion 108 side. Is done. As a result, the rotation member 112, the frame member 114, and the half mirror 38 can be fixed at a desired angle with respect to the left eye image display unit 34 and the right eye image display unit 36.

  The frame member 114 is formed with a groove (not shown) that communicates with the opening of the frame member 114, and the half mirror 38 is held by the frame member 114 by fitting the peripheral edge of the half mirror 38 into the groove. be able to.

  The stereoscopic glasses 40 include a frame 118, a polarizing lens 120 r for the right eye 46 r fixed to the frame 118, and a polarizing lens 120 l for the left eye 46 l fixed to the frame 118.

  Then, the three-dimensional image display device 22A displays a left-eye image 42l including a mammo image 130l indicating the mammo 14 on the display screen 122 of the left-eye image display unit 34, as shown in FIGS. 5, 7A and 7B. In this case, a marker image 76c indicating the marker 70 and a marker image 80c indicating the marker 72 are displayed on the display screen 122 together with the left-eye image 42l. Further, the three-dimensional image display device 22A displays the right eye image 42r including the mammo image 130r indicating the mammo 14 on the display screen 124 of the right eye image display unit 36. In this case, a marker image 76b indicating the marker 70 and a marker image 80b indicating the marker 72 are displayed on the display screen 124 together with the right-eye image 42r.

  As described above, the half mirror 38 transmits the display light 44l of the left-eye image 42l that is a two-dimensional image and outputs the light to the stereoscopic glasses 40 of the observer 20, and displays the right-eye image 42r that is a two-dimensional image. The light 44r is reflected and output to the stereoscopic glasses 40 side. The polarizing lens 120r of the stereoscopic glasses 40 transmits only display light 44r parallel to the absorption axis of the polarizing lens 120r, while the polarizing lens 120l transmits only display light 44l parallel to the absorption axis of the polarizing lens 120l. Let As a result, the observer 20 wearing the stereoscopic glasses 40 sees the right eye image 42r indicated by the display light 44r with the right eye 46r and the left eye image 42l indicated by the display light 44l with the left eye 46l. The three-dimensional image (3D image) 140 shown can be visually recognized.

  In this case, the observer 20 visually recognizes the three-dimensional image 140 displayed on the virtual display screen 144 corresponding to the display screens 122 and 124. The three-dimensional image 140 includes a mammo image 142 of a three-dimensional image display showing the mammo 14 (see FIGS. 1, 3 and 4). In addition to the three-dimensional image 140, marker images 132r and 132l indicating the marker 70 and marker images 134r and 134l indicating the marker 72 are displayed on the virtual display screen 144.

  The marker image 132r is an image in which the marker image 76b is directly reflected on the display screen 144, and the marker image 132l is an image in which the marker image 76c is directly reflected on the display screen 144. The marker image 134r is an image in which the marker image 80b is directly reflected on the display screen 144, and the marker image 134l is an image in which the marker image 80c is directly reflected on the display screen 144.

  As described above, the marker 70 corresponding to the marker images 132r and 132l (76b and 76c) is disposed on the back side (the deepest part) of the mammo 14 along the arrow Z direction with respect to the solid state detector 28. On the other hand, the marker 72 corresponding to the marker images 134r and 134l (80b and 80c) is disposed on the near side (frontmost part) of the mammo 14 along the arrow Z direction with respect to the solid state detector 28. Further, there is a relationship of Δl1 ′> Δl2 ′ between the shift amount Δl1 ′ of the marker images 76b and 76c and the shift amount Δl2 ′ of the marker images 80b and 80c.

  Therefore, when the marker images 76b, 76c, 80b, and 80c are imprinted on the display screen 144 and the marker images 132r, 132l, 134r, and 134l are displayed together with the three-dimensional image 140 (the mammo image 142), the marker 72 corresponds to the marker 72. The marker images 134r and 134l are displayed on the front side (frontmost part) along the depth direction of the three-dimensional image 140 (the mammo image 142), while the marker images 132r and 132l corresponding to the marker 70 are displayed on the mammo. The image 142 is displayed on the back side (the backmost part) along the depth direction. In addition, on the virtual display screen 144, between the deviation amount Δl1 between the marker images 132r and 132l corresponding to the deviation amount Δl1 ′ and the deviation amount Δl2 between the marker images 134r and 134l corresponding to the deviation amount Δl2 ′. , Δl1> Δl2 holds.

  The depth direction of the three-dimensional image 140 (the mammo image 142) refers to the thickness direction of the mammo image 142 and corresponds to the arrow Z direction as the thickness direction of the mammo 14 described above. Further, as described above, in the first embodiment, at least one of the two markers 70 and 72 only needs to be disposed on the mammography apparatus 18A. Of the marker images 132r, 132l, 134r, and 134l, at least the marker images 132r and 132l or the marker images 134r and 134l may be displayed.

  Further, in FIG. 7C, the marker images 132r, 132l, 134r, and 134l are displayed outside the mammo image 142, but are displayed inside the mammo image 142 within a range that does not hinder the interpretation diagnosis by the observer 20. You may be made to do. In this case, the markers 70 and 72 may be arranged at predetermined positions in the mammography apparatus 18A such that the marker images 132r, 132l, 134r, and 134l are displayed inside the mammography image 142.

  FIG. 8 is a detailed block diagram of the radiographic image capturing system 10A.

  Here, it demonstrates centering on the component which was not demonstrated in FIGS. 1-7C.

  The mammography apparatus 18A further includes an imaging condition storage unit 150, a radiation source drive control unit 152, a detector control unit 154, an image information storage unit 156, and a compression plate drive control unit 158.

  The imaging condition storage unit 150 includes a tube current and a tube voltage of the radiation source 26, irradiation doses and irradiation times of the radiations 16b and 16c, imaging angles (+ θ1, −θ1) during stereo imaging, an imaging sequence, and a radiation source at the imaging angle. Imaging conditions including 26 three-dimensional positions (distance between the radiation source 26 and the solid state detector 28) and the like are stored. The imaging conditions can be set (stored) in the imaging condition storage unit 150 due to the operation of the display operation unit 64 by a doctor or an engineer (observer 20). The radiation source drive control unit 152 drives and controls the radiation source 26 according to the imaging conditions. The compression plate drive control unit 158 moves the compression plate 32 in the arrow Z direction. The detector control unit 154 controls the solid state detector 28 and stores the right eye image 42r and the left eye image 42l respectively converted from the radiations 16b and 16c by the solid state detector 28 in the image information storage unit 156.

  The three-dimensional image display device 22A further includes a control unit (display control unit) 160, an image processing unit 162, and an image information storage unit 164.

  The control unit 160 acquires the right eye image 42r and the left eye image 42l stored in the image information storage unit 156, and causes the image processing unit 162 to perform predetermined image processing. Further, the control unit 160 displays the left-eye image 42l after image processing on the display screen 122 (see FIG. 5) of the left-eye image display unit 34, and the right-eye image 42r after image processing is displayed on the display screen of the right-eye image display unit 36. 124 is displayed. Furthermore, the control unit 160 can also execute processing according to the operation input of the operation unit 116 by the observer 20. The image information storage unit 164 stores the right eye image 42r and the left eye image 42l after image processing.

  The configuration of the radiographic image capturing system 10A including the three-dimensional image display device 22A and the mammography device 18A according to the first embodiment is as described above.

  Next, the operation of the radiographic image capturing system 10A (a three-dimensional image display method implemented in the three-dimensional image display device 22A) will be described with reference to the flowchart of FIG.

  In step S1, a doctor or an engineer (observer 20) operates the display operation unit 64 of the mammography apparatus 18A to perform shooting before stereo shooting of the mammo 14 of the subject 12 (see FIGS. 1 to 4 and 8). Shooting conditions corresponding to the mammo 14 are stored in the condition storage unit 150.

  In step S <b> 2, the doctor or engineer inserts the proximal end portion of the compression plate 32 into the groove portion 60 and engages with the mounting portion, whereby the compression plate 32 is interposed between the radiation source accommodation portion 56 and the imaging table 30. Is disposed.

  In step S <b> 3, the doctor or engineer positions the mammo 14 of the subject 12. That is, the doctor or engineer arranges the mammo 14 at a position facing the compression plate 32 on the imaging table 30, and then operates the display operation unit 64 to drive the compression plate drive control unit 158 along the arrow Z direction. The compression plate 32 is moved toward the imaging table 30. As a result, the mammo 14 is compressed and fixed by the imaging table 30 and the compression plate 32.

  In this way, in step S4 after the preparation for imaging in steps S1 to S3 is completed, the mammography apparatus 18A drives the radiation source 26 to perform stereo imaging on the mammo 14.

  In this case, when a doctor or an engineer operates the display operation unit 64 to instruct the start of stereo imaging, the radiation source drive control unit 152 rotates the radiation source storage unit 56 around the hinge unit 58, and the B position The radiation source 26 is disposed on the surface. Next, when a doctor or an engineer operates an exposure switch (not shown) displayed on the display operation unit 64, the radiation source drive control unit 152 is arranged at the B position according to the imaging conditions stored in the imaging condition storage unit 150. The radiation source 26 is driven and controlled.

  As a result, the radiation 16b output from the radiation source 26 at the B position is irradiated to the mammo 14 via the compression plate 32, and the radiation 16b transmitted through the mammo 14 is transmitted to the first radiation image (by the solid detector 28). It is detected as a right eye image 42r). A marker 70 is disposed below the compression plate 32, and a marker 72 is disposed between the solid state detector 28 in the imaging table 30 and the upper surface of the imaging table 30, so that the marker of the radiation 16b is a marker. The radiations 74b and 78b irradiated to the 70 and 72, respectively, are absorbed by the markers 70 and 72. As a result, the projected images of the markers 70 and 72 appear in the right eye image 42r as the marker images 76b and 80b, respectively.

  The detector control unit 154 controls the solid state detector 28 to acquire the first radiation image (right eye image 42r), and temporarily stores the acquired right eye image 42r in the image information storage unit 156.

  At the time when the imaging of the right eye image 42r at the B position is completed, the mammography apparatus 18A moves the radiation source 26 to the C position, and in the same way as the imaging at the B position described above, The radiograph of the first sheet is taken.

  In this case, when a notification of completion of imaging of the right eye image 42r is displayed on the display operation unit 64, the doctor or engineer operates the display operation unit 64 to instruct the start of imaging of the second radiation image.

  The radiation source drive control unit 152 rotates the radiation source storage unit 56 around the hinge unit 58 according to the imaging start instruction, and arranges the radiation source 26 from the B position to the C position. Next, when a doctor or an engineer operates the exposure switch of the display operation unit 64, the radiation source drive control unit 152 controls driving of the radiation source 26 arranged at the position C according to the imaging conditions.

  As a result, the radiation 16c output from the radiation source 26 at the C position is irradiated to the mammo 14 via the compression plate 32, and the radiation 16c transmitted through the mammo 14 is transmitted to the second radiation image ( It is detected as a left eye image 42l). Even in this case, among the radiation 16c, the radiations 74c and 78c irradiated to the markers 70 and 72 are absorbed by the markers 70 and 72, so that the projected images of the markers 70 and 72 are the left eye as the marker images 76c and 80c. Each is reflected in the image 42l. The detector control unit 154 controls the solid state detector 28 to acquire the second radiation image (left eye image 42l), and temporarily stores the acquired left eye image 42l in the image information storage unit 156.

  Accordingly, at the time when the stereo photographing in step S4 is completed, the two pieces of radiation images (the right-eye image 42r and the left-eye image 42l as two-dimensional images) are stored in the image information storage unit 156, respectively.

  In this manner, in step S5 after the completion of stereo shooting in the mammography apparatus 18A, the control unit 160 of the three-dimensional image display apparatus 22A (see FIGS. 1, 5, 6, and 8) is controlled by the observer 20. Based on the radiographic image acquisition instruction resulting from the operation of the operation unit 116 or automatically, the right eye image 42r and the left eye image 42l are acquired from the image information storage unit 156 of the mammography apparatus 18A, and the acquired right eye image 42r and The left-eye image 42l is output to the image processing unit 162. The image processing unit 162 performs predetermined image processing on the right eye image 42r and the left eye image 42l, and stores the right eye image 42r and the left eye image 42l after image processing in the image information storage unit 164 via the control unit 160.

  In the next step S <b> 6, the control unit 160 displays the left eye image 42 l on the display screen 122 of the left eye image display unit 34 and displays the right eye image 42 r on the display screen 124 of the right eye image display unit 36. Accordingly, the display light 44l of the left eye image 42l displayed on the display screen 122 travels obliquely upward toward the half mirror 38, and the display light 44r of the right eye image 42r displayed on the display screen 124 It progresses downward toward 38 (see FIG. 6).

  The half mirror 38 transmits the display light 44l and outputs it to the viewer's 20 stereoscopic glasses 40 side, and reflects the display light 44r to output it to the stereoscopic glasses 40 side. Thereby, the polarizing lens 120r of the stereoscopic glasses 40 transmits only the display light 44r parallel to the absorption axis of the polarizing lens 120r, and the polarizing lens 120l only displays the display light 44l parallel to the absorption axis of the polarizing lens 120l. Make it transparent. As a result, the observer 20 wearing the stereoscopic glasses 40 sees the right eye image 42r indicated by the display light 44r with the right eye 46r and the left eye image 42l indicated by the display light 44l with the left eye 46l. The three-dimensional image 140 (see FIG. 7C) can be easily visually recognized.

  In this case, the marker images 76b and 80b (see FIG. 7A) of the right-eye image 42r are directly reflected on the three-dimensional image 140 including the mammo image 142 of the three-dimensional image display showing the mammo 14 and displayed as the marker images 132r and 134r. At the same time, the marker images 76c and 80c (see FIG. 7B) of the left-eye image 42l are displayed as they are and displayed as the marker images 132l and 134l (see FIG. 7C). Therefore, the observer 20 can visually recognize the marker images 132r, 132l, 134r, and 134l simultaneously with the mammo image 142 of the three-dimensional image 140.

  At that time, the marker images 134r and 134l corresponding to the marker 72 (the marker images 80b and 80c) are displayed on the front side (frontmost part) along the depth direction of the three-dimensional image 140 (the mammo image 142). Thus, the marker images 132r and 132l corresponding to the marker 70 (marker images 76b and 76c thereof) are displayed on the back side (the deepest part) along the depth direction of the mammo image 142.

  Thereby, the observer 20 recognizes the frontmost part and the deepest part of the mammo image 142 using these marker images 132r, 132l, 134r, and 134l as a clue (support), and sets the depth range of the mammo image 142. I can grasp it. Moreover, since there is a relationship of Δl1> Δl2 between the shift amount Δl1 between the marker images 132r and 132l and the shift amount Δl2 between the marker images 134r and 134l, which of the marker images 132r, 132l, 134r, and 134l is It is possible to easily determine whether it is the front side or the back side of the mammo image 142, and as a result, it becomes easier to grasp the space for the mammo image 142.

  As described above, according to the three-dimensional image display device 22A and the three-dimensional image display method according to the first embodiment, the near side and the back along the depth direction of the three-dimensional image 140 (the mammo image 142). Marker images 132r, 132l, 134r, and 134l appearing together with the three-dimensional image 140 are displayed on at least one of the sides.

  Accordingly, the observer 20 can clearly recognize the depth range of the three-dimensional image 140 (the mammo image 142) by visually recognizing the marker images 132r, 132l, 134r, and 134l. It becomes easy to grasp the space. That is, the observer 20 easily uses the marker images 132r, 132l, 134r, and 134l as a support for visually recognizing the three-dimensional image 140 so that the near side and the far side of the three-dimensional image 140 can be easily viewed. It is possible to grasp and clearly recognize the depth range of the three-dimensional image 140. As a result, when visually recognizing the three-dimensional image 140, the line of sight of the observer 20 is stabilized, and the fatigue feeling of the observer 20 can be reduced.

  Therefore, according to the first embodiment, by displaying the marker images 132r, 132l, 134r, and 134l on the near side or the far side of the three-dimensional image 140, the near side and the far side along the depth direction of the three-dimensional image 140 are displayed. It is possible to easily grasp the side, stabilize the viewpoint of the observer 20, and reduce the fatigue of the observer 20.

  In this case, by displaying the marker images 132r, 132l, 134r, and 134l on at least one of the frontmost part and the deepest part along the depth direction of the three-dimensional image 140, the line of sight of the observer 20 can be stabilized and fatigued. It is possible to easily reduce the feeling.

  In addition, when noise is present in the right eye image 42r and the left eye image 42l, since the viewing angles are usually not uniform, the noise is not stereoscopically viewed. However, although there is a slight amount of noise, there is a case in which there is a relationship that is stereoscopically viewed. At this time, the noise also appears on the stereoscopic image (three-dimensional image 140). In the diagnostic interpretation, small points are also diagnosed, so it is desirable that the noise can be reduced as much as possible. Such noise is deeper (back side) than the deepest part where the marker images 132r and 132l are displayed, or shallower (front side) than the frontmost part where the marker images 134r and 134l are displayed. If there is, the noise can be removed.

  Further, if the marker images 132r, 132l, 134r, and 134l are respectively displayed on both the near side and the far side along the depth direction of the three-dimensional image 140, the observer 20 can visually recognize the three-dimensional image 140. Since it becomes easy to feel a volume feeling (depth feeling) with respect to the mammo image 142 of the three-dimensional image 140, it is possible to further stabilize the line of sight of the observer 20 and further reduce fatigue.

  Further, the right eye image display unit 36 displays the right eye image 42r including the marker images 76b and 80b, and the left eye image display unit 34 displays the left eye image 42l including the marker images 76c and 80c. The images 132r, 132l, 134r, and 134l can be displayed reliably. Thereby, since two marker images are displayed on the near side and the back side along the depth direction of the three-dimensional image 140, the observer 20 can easily recognize the depth range of the three-dimensional image 140.

  Furthermore, markers 70 and 72 are arranged between the radiation source 26 and the mammo 14 or between the mammo 14 and the solid state detector 28, and the images of the markers 70 and 72 are marker images when irradiated with the radiation 16b and 16c. Marker images 132r, 132l, 134r, and 134l corresponding to the marker images 76b, 76c, 80b, and 80c can be easily obtained by including them in the right eye image 42r and the left eye image 42l as 76b, 76c, 80b, and 80c, respectively. it can.

  Further, when the observer 20 who is a doctor interprets the right-eye image 42r and the left-eye image 42l obtained by stereo shooting or the three-dimensional image 140, image diagnosis is performed in the following order, and the following further diagnosis is performed. A remarkable effect can be obtained.

  First, the observer 20 performs a diagnostic interpretation of the right eye image 42r and the left eye image 42l. In this case, marker images 76b, 76c, 80b, and 80c are displayed in the right eye image 42r and the left eye image 42l. Therefore, even when the three-dimensional image 140 is displayed and the marker images 132r, 132l, 134r, and 134l corresponding to the marker images 76b, 76c, 80b, and 80c are displayed together with the mammo image 142, the observer 20 It is possible to perform image interpretation diagnosis on the three-dimensional image 140 using the marker images 132r, 132l, 134r, and 134l as clues.

  Next, the doctor makes a diagnostic interpretation of the three-dimensional image 140. In this case, since the marker images 132r, 132l, 134r, and 134l are displayed together with the mammo image 142 in the three-dimensional image 140, the depth range of the mammo image 142 can be easily recognized and the marker images 132r, 132l, and 134r are recognized. , 134l becomes support for stabilizing the viewpoint of the observer 20 during the interpretation diagnosis. As a result, the stability of the line of sight of the observer 20 and the feeling of fatigue during the interpretation diagnosis can be reduced, so that the diagnostic performance for the three-dimensional image 140 can be improved.

  Furthermore, since the markers 70 and 72 have a shape different from that of the mammo 14 and can absorb the radiations 16b and 16c, when the observer 20 performs an interpretation diagnosis on the three-dimensional image 140, the mammo image 142 and the marker The images 132r, 132l, 134r, and 134l can be easily distinguished.

  7A to 7C, as an example, the marker images 76b, 76c, 132r, and 132l (the corresponding marker 70) have a triangular shape, and the marker images 80b, 80c, 134r, and 134l Although the case where the shape of the marker 72) is spherical is illustrated, the first embodiment is not limited to this example, and can be changed to FIGS. 10A and 10B.

  FIG. 10A illustrates a case where rectangular marker images 170 r and 170 l corresponding to the marker 70 and linear marker images 172 r and 172 l corresponding to the marker 72 are displayed on the three-dimensional image 140. FIG. 10B illustrates a case where frame-shaped marker images 174r and 174l corresponding to the markers 70 and ring-shaped marker images 176r and 176l corresponding to the markers 72 are displayed on the three-dimensional image 140. . Also in these modified examples, the above-described effects can be easily obtained.

  1 to 10B, the stereo shooting with respect to the mammo 14 has been described. However, as shown in FIGS. 11A to 12C, the first embodiment can be applied to general shooting (chest shooting) with respect to the subject 180. is there.

  In this case, stereo imaging is performed in a state where the subject 180 is disposed between the imaging table 184 that houses the solid state detector 182 and the radiation source 186.

  In this case, the radiation source 186 is arranged at the E position rotated by an angle of + θ1 with respect to the D position (θ = 0 °) of the central axis 194, and the subject 180 is irradiated with the radiation 188e. On the other hand, the radiation source 186 is arranged at the F position rotated by an angle of −θ1 to irradiate the subject 180 with the radiation 188f.

  The subject 180 is within the irradiation range of the radiation 188e and 188f, and the marker 190 is attached to the position on the radiation source 186 side (the back of the subject 180), while on the other hand, within the irradiation range of the radiation 188e and 188f. Thus, a marker 192 is attached to the position on the imaging table 184 side (the chest of the subject 180).

  Therefore, when the subject 180 is irradiated with the radiation 188e from the radiation source 186 disposed at the E position, the radiation 196e irradiated to the marker 190 among the radiation 188e is absorbed by the marker 190, and as a result. The projected image of the marker 190 appears in the right eye image 210r as a marker image 198e (see FIG. 12A). Of the radiation 188e, the radiation 200e irradiated to the marker 192 is absorbed by the marker 192. As a result, the projected image of the marker 192 is reflected in the right eye image 210r as the marker image 202e. In FIG. 12A, the right eye image 210r is a two-dimensional image including a chest image 212r of the subject 180.

  On the other hand, when the subject 180 is irradiated with the radiation 188f from the radiation source 186 arranged at the position F, the radiation 196f irradiated to the marker 190 among the radiation 188f is absorbed by the marker 190, and as a result. The projected image of the marker 190 appears in the left eye image 210l as a marker image 198f (see FIG. 12B). Of the radiation 188f, the radiation 200f irradiated to the marker 192 is absorbed by the marker 192. As a result, the projected image of the marker 192 appears in the left eye image 210l as the marker image 202f. In FIG. 12B, the left-eye image 210l is a two-dimensional image including a chest image 212l of the subject 180.

  As a result, the observer 20 wearing the stereoscopic glasses 40 (see FIG. 5 and FIG. 6) views the right eye image 210r with the right eye 46r and the left eye image 210l with the left eye 46l. When the image 218 is viewed, the chest image 220 corresponding to the chest images 212r and 212l is displayed on the virtual display screen 144, and the marker images 198e, 198f, 202e, and 202f are reflected on the display screen 144 as they are. The marker images 214r, 214l, 216r, and 216l are also displayed. In FIG. 12C, the relationship Δl3> Δl4 is also established between the shift amount Δl3 between the marker images 214r and 214l and the shift amount Δl4 between the marker images 216r and 216l.

  Even in such stereo shooting in general shooting, the marker images 214r, 214l, 216r, and 216l are reflected in the three-dimensional image 218 at the time of interpretation of the three-dimensional image 218 (the chest image 220). Similarly to the above-described interpretation diagnosis for the three-dimensional image 140 of the mammo 14, the diagnostic performance for the subject 180 can be improved.

  In the first embodiment described above, the markers 70, 72, 190, 192 are arranged in the vicinity of the mammo 14 or the subject 180, and the radiation 16 b, 16 c is irradiated to the mammo 14 and the markers 70, 72, or the subject 180 and markers 190 and 192 are irradiated with radiation 188e and 188f, resulting in three-dimensional images 140 and 218 and marker images 132r, 132l, 134r, 134l, 170r, 170l, 172r, 172l, and 174r. 174 l, 176 r, 176 l, 214 r, 214 l, 216 r, 216 l were obtained. That is, in the first embodiment, the marker images 132r, 132l, 134r, 134l, 170r, 170l, 172r, 172l, and 174r are provided by arranging the markers 70, 72, 190, and 192 on the mammography apparatus 18A in hardware. 174l, 176r, 176l, 214r, 214l, 216r, 216l.

  Next, instead of the hardware markers 70, 72, 190, and 192, a virtual marker is set in software, and a marker image is generated based on the virtual marker and is combined with the three-dimensional image. A technique for displaying (second embodiment) will be described. That is, a radiographic image capturing system 10B including the three-dimensional image display device 22B and the mammography device 18B according to the second embodiment will be described with reference to FIGS. In the description of FIGS. 13 to 15, the same components as those in the first embodiment are denoted by the same reference numerals, and detailed description thereof is omitted.

  As shown in FIG. 13, the mammography apparatus 18B is not provided with markers 70, 72 (see FIGS. 2 to 4 and 8) and markers 190, 192 (see FIGS. 11A and 11B). Of course, neither the right-eye image 42r nor the left-eye image 42l stored in the image information storage unit 156 contains a marker image. The mammography apparatus 18 </ b> B further includes a compression plate position information calculation unit 230 that calculates the position of the compression plate 32 with respect to the imaging table 30. Since the position of the compression plate 32 when the mammo 14 is compressed and held by the compression plate 32 and the imaging table 30 indicates the thickness d of the mammo 14 in the compression holding state, the compression plate position information calculation unit 230 The calculated position of the compression plate 32 (the thickness d of the mammo 14) is output to the control unit 160.

  The three-dimensional image display device 22B further includes a marker position deviation amount calculation unit 232. The control unit 160 acquires the position of the compression plate 32 from the compression plate position information calculation unit 230, and also includes the imaging angles + θ1 and −θ1 included in the imaging conditions from the imaging condition storage unit 150, the radiation source 26, the solid detector 28, and the like. Is also obtained, and the obtained information is output to the marker position deviation amount calculation unit 232.

  Based on the position of the compression plate 32 (the thickness d of the mammo 14), the photographing angles + θ1, −θ1, and the distance L, the marker position deviation amount calculation unit 232 includes a deviation amount Δl1 ′ between the marker images 76b and 76c, A shift amount Δl2 ′ between the marker images 80b and 80c is obtained. In this case, since the thickness d of the mammo 14 at the time of stereo imaging, the imaging angles + θ1, −θ1 and the distance L, and the sizes of the compression plate 32, imaging platform 30, and solid state detector 28 are known, the amount of marker position deviation As illustrated in FIG. 14, the calculation unit 232 sets a virtual marker 234 corresponding to the marker 70 and a virtual marker 236 corresponding to the marker 72, and sets the set virtual markers 234 and 236 as arrows. While moving in the X direction, the arrow Y direction, and the arrow Z direction, the shift amounts Δl1 ′ and Δl2 ′ at the positions of the moved markers 234 and 236 are calculated. Therefore, the marker position deviation amount calculation unit 232 can calculate the maximum value of the deviation amount Δl1 ′ and the minimum value of the deviation amount Δl2 ′ while moving the virtual markers 234 and 236 in the arrow Z direction. is there.

  Note that the maximum value of the shift amount Δl1 ′ is the maximum when the virtual marker 234 is closest to the mammo 14, that is, the virtual marker 234 is the maximum along the arrow Z direction in the mammo 14 with respect to the solid detector 28. Obtained when located in the back (back side). Further, the minimum value of the shift amount Δl2 ′ is determined when the virtual marker 236 is closest to the mammo 14, that is, when the virtual marker 236 is in front of the solid detector 28 along the arrow Z direction in the mammo 14. Obtained when positioned on the front (front side).

  Further, the marker position deviation amount calculation unit 232 calculates the positions of the marker images 76b and 80b in the right eye image 42r and the positions of the marker images 76c and 80c in the left eye image 42l in addition to the deviation amounts Δl1 ′ and Δl2 ′. Of course.

  Then, the control unit 160 outputs the positions of the marker images 76b, 76c, 80b, and 80c calculated by the marker position deviation amount calculation unit 232 and the deviation amounts Δl1 ′ and Δl2 ′ to the image processing unit 162. Then, the image processing unit 162 is caused to perform image processing for reflecting the marker images 76b and 80b in the right eye image 42r, and to perform image processing for reflecting the marker images 76c and 80c in the left eye image 42l. Further, the control unit 160 displays the right-eye image 42r after image processing on the display screen 124 of the right-eye image display unit 36, and displays the left-eye image 42l after image processing on the display screen 122 of the left-eye image display unit 34.

  Next, the operation (three-dimensional image display method) of the three-dimensional image display device 22B according to the second embodiment will be described with reference to the flowcharts of FIGS.

  In step S7 after step S4, the control unit 160 acquires the right eye image 42r and the left eye image 42l in which the marker image is not reflected from the image information storage unit 156, and the position of the compression plate 32 from the compression plate position information calculation unit 230. Furthermore, the imaging angles + θ1, −θ1 and the distance L between the radiation source 26 and the solid state detector 28 are acquired from the imaging condition storage unit 150. The control unit 160 outputs the acquired right eye image 42 r and left eye image 42 l to the image processing unit 162, while outputting the position of the compression plate 32, the photographing angles + θ 1, −θ 1, and the distance L to the marker position deviation amount calculation unit 232. To do.

  In step S8, the marker position deviation amount calculation unit 232 sets the virtual markers 234 and 236, and moves the set virtual markers 234 and 236 in the arrow X direction, the arrow Y direction, and the arrow Z direction, The displacement amounts Δl1 ′ and Δl2 ′ at the moved positions of the markers 234 and 236 are calculated based on the position of the compression plate 32 (the thickness d of the mammo 14), the photographing angles + θ1, −θ1, and the distance L. In this case, the marker position deviation amount calculation unit 232 also calculates the positions of the marker images 76b and 80b in the right eye image 42r and the positions of the marker images 76c and 80c in the left eye image 42l when the deviation amounts Δl1 ′ and Δl2 ′ are calculated. To do.

  Then, the marker position deviation amount calculation unit 232 calculates the maximum value of the deviation amount Δl1 ′, the positions of the marker images 76b and 76c at the maximum value, and the deviation amount Δl2 ′ from the obtained deviation amounts Δl1 ′ and Δl2 ′. And the positions of the marker images 80b and 80c at the minimum value.

  In the next step S9, the control unit 160 determines whether or not an instruction to display / hide the marker images 132r, 132l, 134r, and 134l resulting from the operation of the operation unit 116 by the observer 20 is received, and the marker When the display instruction of the images 132r, 132l, 134r, and 134l is received (step S9: YES), the maximum value of the deviation amount Δl1 ′ obtained by the marker position deviation amount calculation unit 232, the marker at the maximum value The positions of the images 76b and 76c, the minimum value of the shift amount Δl2 ′, and the positions of the marker images 80b and 80c at the minimum value are output to the image processing unit 162, and the right eye image is output to the image processing unit 162. Image processing for reflecting the marker images 76b and 80b in the lens 42r and the marker images 76c and 80c in the left-eye image 42l are performed. Thereby to perform image processing (step S10). The right eye image 42r and the left eye image 42l after the image processing are stored in the image information storage unit 164.

  Then, the control unit 160 displays the three-dimensional image 140 in which the marker images 132r, 132l, 134r, and 134l shown in FIG. In this case, the marker images 132r, 132l, 134r, and 134l are obtained by directly displaying the marker images 76b, 76c, 80b, and 80c generated based on the virtual markers 234 and 236 described above on the virtual display screen 144. Therefore, the shift amount Δl1 between the marker images 132r and 132l is a maximum value corresponding to the maximum value of the shift amount Δl1 ′ described above, and the shift amount Δl2 between the marker images 134r and 134l is the minimum of the shift amount Δl2 ′ described above. The minimum value according to the value.

  In step S9, when the instruction to hide the marker images 132r, 132l, 134r, and 134l is received (step S9: NO), the control unit 160 determines the maximum value of the deviation amount Δl1 ′ and the maximum value. Each position of the marker images 76b and 76c, the minimum value of the shift amount Δl2 ′, and the output of each position of the marker images 80b and 80c at the minimum value to the image processing unit 162 is not performed, and the marker image is not reflected. Only the three-dimensional image 140 using the right eye image 42r and the left eye image 42l is displayed (step S6).

  As described above, according to the three-dimensional image display device 22B and the three-dimensional image display method according to the second embodiment, the marker position deviation amount calculation unit 232 has the thickness d of the mammo 22, the photographing angle + θ1, − Deviation amounts Δl1 ′ and Δl2 ′ are calculated based on θ1 and the distance L between the radiation source 26 and the solid state detector 28, and the control unit 160 obtains marker images 76b and 80b indicating the deviation amounts Δl1 ′. The reflected right-eye image 42r is displayed on the right-eye image display unit 36, and the left-eye image 42l including the marker images 76c and 80c indicating the shift amount Δl2 ′ is displayed on the left-eye image display unit 34. Accordingly, the marker images 132r, 132l, 134r, and 134l of the shift amounts Δl1 and Δl2 corresponding to the shift amounts Δl1 ′ and Δl2 ′ are displayed together with the three-dimensional image 140. As a result, the observer 20 can efficiently perform an interpretation diagnosis on the three-dimensional image 140.

  Further, since the marker position deviation amount calculation unit 232 calculates the maximum value of the deviation amount Δl1 ′ and the minimum value of the deviation amount Δl2 ′, the three-dimensional image 140 is based on the maximum value of the deviation amount Δl1 ′ (maximum Marker images 132r and 132l (with a shift amount Δl1) are displayed, and marker images 134r and 134l based on the minimum value of the shift amount Δl2 ′ (with a minimum shift amount Δl2) are displayed. Thereby, when the observer 20 visually recognizes the three-dimensional image 140, the observer can easily feel a volume feeling (depth feeling) with respect to the three-dimensional image 140. As a result, it is possible to easily stabilize the line of sight of the observer 20 and reduce fatigue, and to further improve the diagnostic performance for the three-dimensional image 140.

  In addition, since the observer 20 can operate the operation unit 116 to instruct the control unit 160 to display / hide the marker images 132r, 132l, 134r, and 134l, the interpretation diagnosis by the observer 20 is performed more efficiently. It becomes possible.

  In the second embodiment, the control unit 160 changes the shape and / or size of the marker images 76b, 76c, 80b, and 80c based on the shape and / or size of the right eye image 42r and the left eye image 42l. In this way, the image processing unit 162 may be instructed. By further adding such a function to the three-dimensional image display device 22B, it is possible to perform the interpretation diagnosis by the observer 20 more efficiently.

  Further, as described above, the marker position deviation amount calculation unit 232 includes deviation amounts Δl1 ′, Δl2 ′ when the virtual markers 234, 236 are moved in the arrow X direction, the arrow Y direction, and the arrow Z direction, The positions of the marker images 76b, 76c, 80b and 80c corresponding to the deviation amounts Δl1 ′ and Δl2 ′ are calculated. Therefore, the control unit 160 uses the calculation result of the marker position deviation amount calculation unit 232 to determine the positions of the marker images 76b, 76c, 80b, and 80c based on the shape and / or size of the right eye image 42r and the left eye image 42l. It is also possible to instruct the image processing unit 162 to change. Thereby, the positions of the marker images 132r, 132l, 134r, and 134l along the depth direction in the three-dimensional image 140 can be changed, and the interpretation diagnosis by the observer 20 can be performed more efficiently.

  Note that the present invention is not limited to the above-described embodiment, and it is needless to say that various configurations can be adopted without departing from the gist of the present invention.

10A, 10B ... Radiological imaging system 12, 180 ... Subject 14 ... Mammo 16b, 16c, 74b, 74c, 78b, 78c, 188e, 188f, 196e, 196f, 200e, 200f ... Radiation 18A, 18B ... Mammography device 20 ... Observation 22A, 22B ... three-dimensional image display devices 26, 186 ... radiation sources 28, 182 ... solid state detectors 30, 184 ... imaging table 32 ... compression plate 34 ... left eye image display unit 36 ... right eye image display unit 38 ... half mirror 40 ... stereoscopic glasses 42l, 210l ... left eye images 42r, 210r ... right eye images 44l, 44r ... display light 46l ... left eyes 46r ... right eyes 70, 72, 190, 192, 234, 236 ... markers 76b, 76c, 80b, 80c, 132l 132r, 134l, 134r, 170l, 170r, 172l, 72r, 174l, 174r, 176l, 176r, 198e, 198f, 202e, 202f, 214l, 214r, 216l, 216r ... marker image 107 ... half mirror support mechanism 116 ... operation unit 120r, 120l ... polarizing lenses 122, 124, 144 ... Display screens 130l, 130r, 142 ... mammo images 140, 218 ... three-dimensional image 150 ... imaging condition storage unit 160 ... control units 212l, 212r ... chest image 230 ... compression plate position information calculation unit 232 ... marker position deviation amount calculation unit

Claims (14)

A right-eye image display unit that displays a right-eye image that is a two-dimensional image for the right eye of the observer;
A left-eye image display unit that displays a left-eye image that is a two-dimensional image for the left eye of the observer;
A three-dimensional image display unit for allowing the observer to visually recognize a three-dimensional image based on the right-eye image and the left-eye image;
A display control unit that displays on the three-dimensional image display unit a marker image that is displayed together with the three-dimensional image on at least one of the near side and the back side along the depth direction of the three-dimensional image;
A three-dimensional image display device comprising: The apparatus of claim 1.
The three-dimensional image display device, wherein the display control unit displays the marker image on at least one of a frontmost part and a rearmost part along the depth direction of the three-dimensional image. The apparatus according to claim 1 or 2,
The three-dimensional image display device, wherein the display control unit displays the marker images on the near side and the far side along the depth direction of the three-dimensional image, respectively. The device according to any one of claims 1 to 3,
The display control unit displays the right eye image and the right eye marker image on the right eye image display unit, and displays the left eye image and left eye marker image on the left eye image display unit, whereby the three-dimensional image display unit And displaying the three-dimensional image, the right-eye marker image, and the left-eye marker image together. The apparatus of claim 4.
The right eye image is acquired when the radiation detector detects the radiation transmitted through the subject when the radiation source irradiates the radiation detector through the subject from one angle with respect to the radiation detector. One of the radiographs
In the left-eye image, the radiation detector detects the radiation transmitted through the subject when the radiation source irradiates the radiation detector through the subject from the other angle with respect to the radiation detector. Is the other radiation image acquired by
When a marker is disposed between at least one of the radiation source and the subject and between the subject and the radiation detector,
The right-eye marker image is an image of the marker that appears in the one radiation image when the radiation source irradiates the subject and the marker with the radiation from the one angle.
The left-eye marker image is an image of the marker that appears in the other radiation image when the radiation source irradiates the subject and the marker with the radiation from the other angle. Dimensional image display device. The apparatus of claim 5.
The radiation detector is housed in an imaging table that holds the breast of the subject,
The breast is compressed by a compression plate that is displaced from the radiation source side toward the imaging table and the imaging table,
The marker is provided on at least one of the compression plate and between the breast side and the radiation detector in the imaging table,
The three-dimensional image display device, wherein the radiation is irradiated from the radiation source to the radiation detector through the breast in a state where the breast is compressed and held by the compression plate and the imaging table. The apparatus of claim 5.
The radiation detector is housed in a photographing table facing the subject,
The three-dimensional image display device, wherein the marker is arranged on at least one of the radiation source side and the imaging stand side of the subject. In the apparatus of any one of Claims 5-7,
The three-dimensional image display device, wherein the marker has a shape different from that of the subject and can absorb the radiation. The apparatus of claim 4.
The right eye image is acquired when the radiation detector detects the radiation transmitted through the subject when the radiation source irradiates the radiation detector through the subject from one angle with respect to the radiation detector. One of the radiographs
In the left-eye image, the radiation detector detects the radiation transmitted through the subject when the radiation source irradiates the radiation detector through the subject from the other angle with respect to the radiation detector. Is the other radiation image acquired by
The three-dimensional image display device includes the right eye marker image and the left eye based on the thickness of the subject, the one angle, the other angle, and the distance between the radiation source and the radiation detector. A displacement amount calculation unit for calculating a displacement amount from the marker image for use,
The display control unit causes the right-eye image display unit to display the right-eye marker image based on the shift amount, and causes the left-eye image display unit to display the left-eye marker image. Image display device. The apparatus of claim 9.
The shift amount calculation unit calculates a minimum shift amount when the right eye marker image and the left eye marker image are displayed on the forefront along the depth direction, and / or the right eye marker image and A three-dimensional image display device that calculates a maximum shift amount when the left-eye marker image is displayed in the innermost portion along the depth direction. The apparatus according to claim 9 or 10,
The display control unit further includes a display instruction unit that instructs the display control unit to display the right eye marker image on the right eye image display unit and whether to display the left eye marker image on the left eye image display unit. A three-dimensional image display device. The device according to any one of claims 9 to 11,
The display control unit can change the shape and / or size of the right-eye marker image and the left-eye marker image based on the shape and / or size of the right-eye image and the left-eye image. A three-dimensional image display device. The apparatus according to any one of claims 9 to 12,
The display control unit can change a display position of the right eye marker image and the left eye marker image along the depth direction based on the shape and / or size of the right eye image and the left eye image. A three-dimensional image display device. A right eye image that is a two-dimensional image for the right eye of the observer is displayed on the right eye image display unit, a left eye image that is a two-dimensional image for the left eye of the observer is displayed on the left eye image display unit, and the right eye When the observer visually recognizes a three-dimensional image based on the image and the left-eye image by a three-dimensional image display unit,
A marker image displayed together with the three-dimensional image is displayed on the three-dimensional image display unit on at least one of the near side and the back side along the depth direction of the three-dimensional image. .

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