WO2012102022A1 - Procédé d'affichage d'image stéréoscopique, et programme et appareil de commande d'affichage d'image stéréoscopique - Google Patents

Procédé d'affichage d'image stéréoscopique, et programme et appareil de commande d'affichage d'image stéréoscopique Download PDF

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Publication number
WO2012102022A1
WO2012102022A1 PCT/JP2012/000425 JP2012000425W WO2012102022A1 WO 2012102022 A1 WO2012102022 A1 WO 2012102022A1 JP 2012000425 W JP2012000425 W JP 2012000425W WO 2012102022 A1 WO2012102022 A1 WO 2012102022A1
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Prior art keywords
radiation
display
image
subject
stereoscopic
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PCT/JP2012/000425
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English (en)
Japanese (ja)
Inventor
孝夫 桑原
靖子 八尋
大田　恭義
玲 長谷川
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富士フイルム株式会社
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Publication of WO2012102022A1 publication Critical patent/WO2012102022A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/022—Stereoscopic imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/502—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of breast, i.e. mammography
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N13/00—Stereoscopic video systems; Multi-view video systems; Details thereof
    • H04N13/10—Processing, recording or transmission of stereoscopic or multi-view image signals
    • H04N13/106—Processing image signals
    • H04N13/128—Adjusting depth or disparity
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N13/00—Stereoscopic video systems; Multi-view video systems; Details thereof
    • H04N13/10—Processing, recording or transmission of stereoscopic or multi-view image signals
    • H04N13/106—Processing image signals
    • H04N13/139—Format conversion, e.g. of frame-rate or size

Definitions

  • the present invention is a technique for irradiating a subject with radiation from two different imaging directions, detecting a radiographic image for each imaging direction, and displaying a stereoscopic image using the two detected radiographic images.
  • the present invention relates to a technique for displaying an enlarged stereoscopic image by enlarging at least a part of a range in a radiation image.
  • stereoscopic viewing can be performed using parallax by displaying a combination of a plurality of images.
  • a stereoscopically viewable image hereinafter referred to as a stereoscopic image or a stereo image
  • a stereoscopic image or a stereo image is generated based on a plurality of images having parallax obtained by photographing the same subject from different directions.
  • Such generation of stereoscopic images is used not only in fields such as digital cameras and televisions but also in medical fields such as radiological diagnostic equipment and endoscopy equipment.
  • a subject is irradiated with radiation from different directions, and the radiation transmitted through the subject is detected by a radiation image detector, and a plurality of radiation images having parallax are obtained. Acquiring and generating a stereoscopic image based on these radiation images is performed. And by generating a stereoscopic image in this way, a radiographic image with a sense of depth can be observed, and a radiographic image more suitable for diagnosis can be observed.
  • the region of interest in the subject is enlarged and displayed on the stereoscopic image.
  • display parameters of the stereoscopic display are acquired in advance so that stereoscopic viewing is not possible, so as not to exceed the allowable range of fusion of the observer or the display stereoscopic limit range of the stereoscopic display. It has also been proposed to narrow the distance between the radiation sources (Patent Document 2).
  • Patent Document 1 when the technique described in Patent Document 1 is used, it is impossible to avoid the stereoscopic image popping forward from before the enlargement although the stereoscopic view is maintained during the enlarged display.
  • Patent Document 2 cannot be applied to images that have already been taken.
  • the present invention avoids the stereoscopic image from being greatly projected forward when displaying at least a part of the two radiographic images constituting the stereoscopic image in an enlarged manner. It is an object of the present invention to provide a stereoscopic display method, a stereoscopic display control device, and a program that can reduce the burden on the user.
  • the stereoscopic image display method of the present invention includes a step of performing a stereoscopic display based on two radiographic images formed by a radiographic image detector detecting radiation irradiated to a subject from two different shooting directions.
  • the position corresponding to each other in the two radiographic images corresponding to the position of the foreground of the subject at the time is specified, and the stereoscopic display is performed based on the specified position
  • the stereoscopic image display control apparatus of the present invention performs stereoscopic display based on two radiographic images formed by a radiographic image detector detecting radiation irradiated to a subject from two different imaging directions.
  • a first display control unit an imaging condition acquisition unit for acquiring imaging condition information capable of specifying a distance relationship between a radiation image detector, a subject, and a radiation source when two radiographic images are formed; and two radiations
  • An enlargement target area acquisition unit that acquires information representing enlargement target areas corresponding to each other in the image, and an enlargement that generates an enlarged radiographic image obtained by enlarging the acquired enlargement target area to a given size from each of the two radiographic images
  • positions corresponding to each other in the two radiographic images corresponding to the position of the foreground of the subject when viewed from the radiation source
  • the display position of the enlarged radiation image is set so that the foremost position of the enlargement target area in the stereoscopic
  • a stereoscopic image display device is characterized in that the stereoscopic image display control device and a stereoscopic display unit for performing stereoscopic display of a subject are provided.
  • the stereoscopic image display control program of the present invention displays on a computer a stereoscopic display based on two radiographic images formed by a radiographic image detector detecting radiation applied to a subject from two different imaging directions.
  • a step of causing the display unit to perform a step of acquiring imaging condition information capable of specifying a distance relationship between the radiation image detector, the subject, and the radiation source at the time of forming the two radiation images;
  • a step of determining the display position of the enlarged radiation image based on the determined position so that the foremost position of the enlargement target area in the stereoscopic display space where the stereoscopic display is performed matches the forefront position of the
  • the photographing condition information is preferably information including information on the thickness of the subject.
  • the compression thickness of the breast can be used as information on the thickness of the subject.
  • the enlargement target area may be a part of the original radiation image or the whole.
  • the enlargement target area may be designated by a user's manual operation, or may be automatically designated using a known image recognition process (for example, an abnormal shadow detection process). .
  • imaging condition information capable of specifying a distance relationship between a radiographic image detector, a subject, and a radiation source at the time of forming two radiographic images for stereoscopic display is acquired, and the two radiographic images are mutually connected.
  • the position of the forefront of the display object does not change before and after the enlarged display of the original radiation image, it is possible to prevent the entire image from approaching the depth direction forward by the enlarged display, Before and after the enlarged display, the observer does not need to readjust the focal length and convergence, so that the physical burden such as eye fatigue of the observer is reduced. This is particularly effective for an interpreting doctor who observes a large amount of images.
  • FIG. 1 is a schematic configuration diagram of a breast image photographing display system using an embodiment of a stereoscopic image display device of the present invention.
  • the figure which looked at the arm part of the mammography display system shown in FIG. 1 from the right direction of FIG. 1 is a block diagram showing a schematic configuration inside a computer of the breast image capturing and displaying system shown in FIG.
  • the figure which showed an example of the radiographic image for right eyes, and the radiographic image for left eyes typically The figure which shows an example of the stereo image of the breast containing an abnormal shadow typically The figure which shows typically an example of expansion object range R1 and expansion object range R2 The figure for demonstrating the shift process performed to the enlarged radiation image for right eyes, and the enlarged radiation image for left eyes. The figure for demonstrating pop-out amount (DELTA) DF of a stereo image Graph showing an example of the relationship between binocular parallax ⁇ P and pop-out amount ⁇ DF The figure which shows typically the positional relationship of the radiation source at the time of imaging
  • FIG. 1 is a diagram showing a schematic configuration of the entire breast image photographing display system of the present embodiment.
  • a breast image photographing display system 1 includes a breast image photographing device 10, a computer 2 connected to the breast image photographing device 10, and a monitor 3 (display unit) connected to the computer 2. ) And an input unit 4.
  • the mammography apparatus 10 includes a base 11, a rotary shaft 12 that can move in the vertical direction (Z direction) with respect to the base 11, and can rotate.
  • the arm part 13 connected with the base 11 is provided.
  • FIG. 2 shows the arm 13 viewed from the right direction in FIG.
  • the arm section 13 has an alphabet C shape, and a radiation table 16 is attached to one end of the arm section 13 so as to face the imaging table 14 at the other end.
  • the rotation and vertical movement of the arm unit 13 are controlled by an arm controller 31 incorporated in the base 11.
  • a radiation image detector 15 such as a flat panel detector, and a detector controller 33 for controlling reading of a charge signal from the radiation image detector 15 are provided.
  • a charge amplifier that converts the charge signal read from the radiation image detector 15 into a voltage signal
  • a correlated double sampling circuit that samples the voltage signal output from the charge amplifier
  • a circuit board provided with an AD conversion unit for converting a voltage signal into a digital signal is also installed.
  • the photographing table 14 is configured to be rotatable with respect to the arm unit 13, and even when the arm unit 13 rotates with respect to the base 11, the direction of the photographing table 14 is fixed to the base 11. can do.
  • the radiographic image detector 15 can repeatedly perform recording and reading of radiographic images, and a so-called direct conversion type radiographic image detector that directly receives radiation and generates charges may be used.
  • a so-called indirect conversion type radiation image detector that converts radiation once into visible light and converts the visible light into a charge signal may be used.
  • a radiation image signal readout method a radiation image signal is read out by turning on / off a TFT (thin film transistor) switch, or by irradiating reading light. It is desirable to use a so-called optical readout system from which a radiation image signal is read out, but the present invention is not limited to this, and other systems may be used.
  • a radiation source 17 and a radiation source controller 32 are accommodated in the radiation irradiation unit 16.
  • the radiation source controller 32 controls the timing of irradiating radiation from the radiation source 17 and the radiation generation conditions (tube voltage, tube current, time, tube current time product, etc.) in the radiation source 17.
  • a compression plate 18 that is disposed above the imaging table 14 and presses and compresses the breast M, a support portion 20 that supports the compression plate 18, and a support portion 20 that extends in the vertical direction.
  • a moving mechanism 19 for moving in the (Z direction) is provided. The position and compression thickness of the compression plate 18 are controlled by the compression plate controller 34 and output to the computer 2.
  • the computer 2 includes a central processing unit (CPU) and a storage device such as a semiconductor memory, a hard disk, and an SSD, and controls as shown in FIG. 3 by these hardware and software running on the hardware.
  • a unit 8a, a radiation image storage unit 8b, an imaging condition acquisition unit 8c, an image processing unit 8d, and a display control unit 8e are configured.
  • the control unit 8a, the photographing condition acquisition unit 8c, the image processing unit 8d, and the display control unit 8e are realized by executing a program installed from a recording medium such as a CD-ROM.
  • the program may be installed after being downloaded from a storage device of a server connected via a network such as the Internet.
  • the control unit 8a outputs predetermined control signals to the various controllers 31 to 35, controls the flow of processing between the units 8a to 8e in the computer 2, and the monitor 3 and the input unit 4
  • the control of the entire system for realizing the flow of processing in each embodiment shown in FIG. 4 is performed by performing control of data and processing. A specific control method will be described in detail later.
  • the radiation image storage unit 8b stores in advance two radiation images detected by the radiation image detector 15 by photographing from two different photographing directions.
  • Imaging condition acquisition unit 8c is shown in Figure 1, the distance between the radiation source 17 and the radiation image detector 15 (in FIG. 2, the rotation radius of the radiation source 17 around the rotation axis 12) and d 1
  • the distance d 2 between the upper surface of the imaging table 14 on which the subject breast M is placed and the radiation image detector 15 is acquired from the control unit 8a, a setting file or the like, and is shown in FIG.
  • the irradiation angle ( ⁇ ⁇ ′ in the figure) of the radiation source 17 at the time of imaging is acquired from the arm controller 31, and the compression thickness d 3 of the breast M is acquired from the compression plate controller 34.
  • the image processing unit 8d includes an enlargement condition acquisition unit 40, an enlargement processing unit 41, and a shift processing unit 42.
  • the enlargement condition acquisition unit 40 specifies at least a part of the two radiographic images as an enlargement target range and accepts designation of an enlargement ratio for the enlargement target range.
  • the enlargement condition acquisition unit 40 is designated. A position in each radiographic image corresponding to the determined position is specified, and an enlargement target range centering on the specified position is specified.
  • the size of the enlargement target range may be a size set in advance, or may be determined according to the enlargement ratio designated by the observer, or the observer may input the input unit 4. You may make it set using.
  • the stereoscopic cursor is a cursor that is stereoscopically displayed in the stereoscopic display space by displaying a right-eye cursor image and a left-eye cursor image having a predetermined left-right parallax amount on the monitor 3. Similar to the cursor, the image displayed on the monitor 3 can be moved not only in the vertical and horizontal directions, but also in the depth direction connecting the observer and the monitor. This movement in the depth direction is realized by adjusting the amount of parallax between the right-eye cursor image and the left-eye cursor image (for details, see Japanese Patent Application Laid-Open No. 11-039135).
  • the enlargement processing unit 41 performs a process of enlarging the radiation image within the enlargement target range specified by the enlargement condition acquisition unit 40 at an enlargement rate specified by the enlargement condition acquisition unit 40.
  • the enlargement rate of the enlargement process may be a preset value. Note that the enlargement process may enlarge the radiation image for each eye at a specified enlargement ratio, or the enlargement target range displayed stereoscopically on the monitor 3 is enlarged at the specified enlargement ratio. In this way, the radiation image for each eye may be enlarged.
  • the shift processing unit 42 corresponds to the display position determination unit of the present invention, and performs a shift process that relatively shifts the enlarged radiation image subjected to the enlargement process by the enlargement processing unit 41 in the parallax direction. .
  • the shift processing unit 42 expands corresponding to the position of the forefront of the breast M when viewed from the radiation source 17 based on various types of information on the imaging conditions acquired by the imaging condition acquisition unit 8c.
  • the positions corresponding to each other in the previous two radiographic images are specified, and based on the specified positions, the depth position of the forefront of the enlargement target range matches the position of the forefront of the breast M before enlarged display.
  • the shift process is performed with an appropriate shift amount. Details of the specific shift process will be described later.
  • the display control unit 8e performs a predetermined process on the two radiographic images read from the radiographic image storage unit 8b, and then displays a normal radiographic stereo image of the breast M on the monitor 3.
  • the shift processing unit 42 performs a predetermined process on the two enlarged radiation images subjected to the shift process, and then displays the enlargement target on the monitor 3. An enlarged stereo image of the range is displayed.
  • the input unit 4 is composed of a pointing device such as a keyboard and a mouse, for example, and accepts an input of shooting conditions and a shooting start instruction by a photographer, or specifies an enlarged display range as described above. Or the input of the size of the enlargement target range and the enlargement ratio in the enlargement process.
  • the input unit 4 can perform the above-described operation of the three-dimensional cursor, that is, the operation of moving the cursor in the three-dimensional direction.
  • the input unit 4 is used for the movement operation in the depth direction. It is preferable to use a wheel mouse equipped with a rotating wheel.
  • the monitor 3 corresponds to the display unit of the present invention, and is configured to be able to display a stereo image using two radiographic image signals output from the computer 2 when photographing a stereo image. It is.
  • a configuration for displaying a stereo image for example, two radiographic images are displayed using two screens, and one of these radiographic images is incident on the right eye of the observer by using a half mirror or polarizing glass.
  • the other radiation image can be made to enter the left eye of the observer to display a stereo image.
  • two radiographic images may be displayed in a superimposed manner while being shifted by a predetermined amount of parallax, and this may be configured to generate a stereo image by observing with a polarizing glass, or a parallax barrier method and a lenticular method
  • a stereo image may be generated by displaying two radiation images on a stereoscopically viewable 3D liquid crystal.
  • the patient's breast M is placed on the imaging table 14, and the breast M is compressed with a predetermined pressure by the compression plate 18 (S10).
  • the compression plate controller 34 outputs the compression thickness d 3 of the breast M.
  • the first radiographic image of the two radiographic images constituting the stereo image of the breast M is captured (S14).
  • the control unit 8 a reads a convergence angle ⁇ for photographing a preset stereo image, and outputs the read information on the convergence angle ⁇ to the arm controller 31.
  • the convergence angle ⁇ represents an angle formed by the right eye and the left eye when the center of the monitor surface is viewed.
  • the convergence angle ⁇ is twice the irradiation angle ⁇ ′ of the radiation source 17. , That is, an angle twice the angle formed by the radiation irradiation axis with respect to the normal line of the detection surface of the radiation image detector 15.
  • ⁇ ′ 2 ° is stored in advance as information of the irradiation angle ⁇ ′ constituting the convergence angle ⁇ at this time, but is not limited to this, and an arbitrary convergence angle or irradiation is input by the photographer in the input unit 4.
  • the corner can be set.
  • the arm controller 31 receives the information on the convergence angle ⁇ output from the control unit 8a.
  • the arm controller 31 captures the image of the arm unit 13 based on the information on the convergence angle ⁇ as shown in FIG.
  • a control signal is output so as to rotate + ⁇ ′ with respect to the direction perpendicular to the table 14. That is, in the present embodiment, a control signal is output so that the arm unit 13 is rotated + 2 ° with respect to a direction perpendicular to the imaging table 14.
  • the control unit 8a applies radiation to the radiation source controller 32 and the detector controller 33 and the radiation.
  • a control signal is output so as to read out the image signal.
  • radiation is emitted from the radiation source 17
  • a radiation image obtained by photographing the breast from the + 2 ° direction is detected by the radiation image detector 15, and a radiation image signal is read by the detector controller 33.
  • the radiographic image signal is stored in the radiographic image storage unit 8 b of the computer 2.
  • the arm controller 31 outputs a control signal so as to rotate the arm unit 13 by ⁇ ′ with respect to a direction perpendicular to the imaging table 14. That is, in the present embodiment, a control signal is output so that the arm unit 13 is rotated by ⁇ 2 ° with respect to a direction perpendicular to the imaging table 14.
  • the control unit 8 a applies radiation to the radiation source controller 32 and the detector controller 33, and the radiation.
  • a control signal is output so as to read out the image signal.
  • radiation is emitted from the radiation source 17
  • a radiation image obtained by imaging the breast from the ⁇ 2 ° direction is detected by the radiation image detector 15, and a radiation image signal is read by the detector controller 33.
  • predetermined signal processing is performed, it is stored in the radiation image storage unit 8b of the computer 2.
  • FIG. 5 schematically shows a stereo image of the breast M displayed on the monitor 3.
  • the enlargement condition acquisition unit 40 specifies a position in each radiation image corresponding to the designated position, and specifies an enlargement target range centered on the specified position.
  • FIG. 7 schematically shows the enlargement target range R1 and the enlargement target range R2 specified by the enlargement condition acquisition unit 40 for each of the right-eye radiographic image and the left-eye radiographic image. Further, the enlargement condition acquisition unit 40 receives an input of an enlargement rate for the enlargement target range (S20).
  • the enlargement processing unit 41 converts the radiation image within the enlargement target range specified by the enlargement condition acquisition unit 40 into the enlargement condition.
  • An enlarged radiation image for each eye enlarged at an enlargement ratio designated by the acquisition unit 40 is generated (S22).
  • the imaging condition acquisition unit 8c includes a distance 1 between the radiation source 17 and the radiation image detector 15, a distance d 2 between the upper surface of the imaging table 14 and the radiation image detector 15, a compression thickness d 3 , a radiation The irradiation angle ( ⁇ ⁇ ′) of the source 17 is acquired (S24).
  • the enlarged radiation image for each eye generated in the enlargement processing unit 41 is input to the shift processing unit 42, and the shift processing unit 42 shifts relative to the input enlarged radiation image in the parallax direction. Shift processing is performed (S26). In the present embodiment, as shown in FIG. 8, the shift process is performed with a shift amount so that the parallax amount between the right-eye enlarged radiation image and the left-eye enlarged radiation image becomes small.
  • the pop-out amount ⁇ DF of a stereo image is represented by the following formula (1).
  • ⁇ DF ⁇ P ⁇ D / (P + ⁇ P) (1)
  • ⁇ P is the binocular parallax between the right-eye image I 2 and the left-eye image I 1 on the display surface
  • P is the binocular distance of the observer
  • D is the display surface and the observation It is the distance (observation distance) to the person.
  • the distance between the radiation source 17 and the detection surface of the radiation image detector 15 in this embodiment is 65 cm, for example, the parallel movement distance when photographing from ⁇ 2 ° and + 2 ° is about 4.5 cm. . Therefore, if displayed at the same magnification as it is, the binocular parallax is 4.5 cm, and when the observation distance is 30 cm, the pop-out amount is about 12 cm from the graph shown in FIG. For example, when the image is enlarged by 2 times or 3 times, the binocular parallax spreads to 9 cm and 13.5 cm, which greatly exceeds the binocular fusion area. Further, since the measurement object has a thickness, the thickness t corresponding to the object is further added to the pop-out amount, so that the fusion is more difficult.
  • the pop-out amount ⁇ DF is converted by the above equation (1) from the parallax and magnification of the two radiographic images at the time of imaging, and the sum of the product of the subject thickness t and the magnification ( ⁇ DF + t ⁇ magnification) is It is determined whether or not the fusion limit ⁇ Dmax is exceeded, and if it is exceeded, it is desirable to adjust the parallax in a direction lower than ⁇ Dmax. Since the fusion limit ⁇ Dmax differs depending on the individual, it is preferable to display images with different projection amounts in advance and measure the observer's fusion limit ⁇ Dmax.
  • the above examination result is further developed, and the shift processing unit 42 enlarges the depth position (center position of the enlargement target range) in the forefront of the enlargement target range specified by the enlargement condition acquisition unit 40. Shift processing is performed with a shift amount that matches the position of the forefront of the breast M, which is the subject in the radiographic image before display.
  • the shift processing unit 42 first corresponds to the position of the forefront of the breast M when viewed from the radiation source 17 based on various information on the imaging conditions acquired by the imaging condition acquisition unit 8c. The positions corresponding to each other in the two radiographic images before enlargement are specified.
  • FIG. 11 schematically shows the positional relationship among the radiation source 17, the subject breast M, the radiation image detector 15, and the upper surface of the imaging table 14 at the time of imaging.
  • the distance between the radiation source 17 at each position and the radiation image detector 15 is d 1 cos ⁇ ′, and between the radiation sources 17 at both positions. Is 2d 1 sin ⁇ ′.
  • the difference in position at which the foremost point MF of the breast M forms an image on the radiation image detector 15 by irradiation of radiation from the radiation source 17 at each position that is, both the points MF in the radiation image for each eye.
  • the eye parallax ⁇ P MF is obtained by the following equation (2).
  • ⁇ P MF ((d 2 + d 3 ) ⁇ 2d 1 sin ⁇ ′) / (d 1 cos ⁇ ′ ⁇ (d 2 + d 3 )) (2) Therefore, when the pixel size of the radiographic image detector 15 and q 1, which represents the binocular disparity [Delta] P MF of points MF in the radiation images for each eye in the number of pixels [Delta] P MF / q 1 (hereinafter, [Delta] P MF ' And).
  • the depth position in the forefront of the enlargement target range (the center position of the enlargement target range) is specified by the three-dimensional cursor in the enlargement condition acquisition unit 40. Therefore, the cursor image for each eye on the monitor 3 is displayed. difference in position, binocular parallax on the monitor 3 of the center position of the enlargement range (hereinafter referred to as [Delta] P ME a illustrates this binocular disparity in pixels) become.
  • the shift processing unit 42 shifts the enlarged radiation image for each eye by
  • the position of the foreground of the subject in the radiographic image before enlarged display can be matched.
  • the enlarged radiographic image subjected to the shift processing in the shift processing unit 42 is output to the display control unit 8e, and the display control unit 8e performs a predetermined process on the input enlarged radiographic image, and then monitors 3 and the enlarged stereo image is displayed on the monitor 3 (S28).
  • the imaging condition acquisition unit 8c includes the radiation image detector 15, the subject M, and the radiation source 17 when two radiation images for stereoscopic display are formed. While acquiring the imaging condition information that can specify the distance relationship, the enlargement condition acquisition unit 8d acquires the information of the enlargement target ranges corresponding to each other in the two radiographic images, and the enlargement processing unit 41 receives each of the two radiographic images.
  • an enlarged radiation image in which the enlargement target range is enlarged to a given size is generated, and the shift processing unit 42 is based on the imaging condition information, and the forefront of the breast M that is the subject when viewed from the radiation source 17
  • the positions corresponding to each other in the two radiographic images corresponding to the position of the position are identified, and based on the identified position, the forefront position of the enlargement target range in the stereoscopic display space where the stereoscopic display is performed ,
  • the display position of the enlarged radiation image is determined so as to match the position of the forefront of the breast M, and the display control unit 8e causes the monitor 3 to display two enlarged radiation images at the determined display position.
  • Stereoscopic display of the enlargement target range can be performed.
  • the position of the forefront of the display object does not change before and after the enlarged display of the original radiation image, it is possible to prevent the entire image from approaching the depth direction forward by the enlarged display, Before and after the enlarged display, the observer does not need to readjust the focal length and convergence, so that the physical burden such as eye fatigue of the observer is reduced. This is particularly effective for an interpreting doctor who observes a large amount of images.
  • the stereoscopic image display device of the present invention is applied to a breast image capturing and displaying system.
  • the subject is not limited to the breast, and the chest other than the breast (heart, lung, etc.) ), Or a radiographic imaging device for so-called general imaging for imaging the head or the like.
  • information on the thickness of the subject in the depth direction may be input by the observer using the input unit 4, for example.
  • the enlargement target range is specified based on an observer's manual designation operation.
  • an abnormal shadow in a subject from a radiographic image for each eye using a known method, etc. The region of interest may be detected, and a region having a predetermined size including the detected region of interest may be set as the enlargement target range.
  • the correspondence relationship between the regions of interest detected in both radiographic images is specified by searching for regions of interest in the vicinity of the same coordinate position as the region of interest in the other radiographic image. can do.
  • the enlargement condition acquisition unit 40 specifies the enlargement target range so that the position designated by the three-dimensional cursor is the frontmost position of the enlargement target range.
  • a cubic region whose position is the center of the enlargement target range may be set as the enlargement target range.
  • the position forward in the depth direction by half the length of the side of the cube from the designated position may be set as the forefront position of the enlargement target range.
  • region centering on the designated position as an expansion object range In this case, the position in front of the depth direction corresponding to the radius of the sphere may be set as the forefront position of the enlargement target range.

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  • Apparatus For Radiation Diagnosis (AREA)

Abstract

Le problème à résoudre dans le cadre de la présente invention consiste à réduire le stress d'un observateur, en empêchant une image stéréoscopique de se décaler vers l'avant de manière excessive lorsqu'au moins une partie de deux radiographies configurant une image stéréoscopique est élargie et affichée. La solution proposée consiste en l'acquisition d'informations d'état d'imagerie, qui peuvent spécifier les relations de distance entre un détecteur de radiographie, un sujet, et une source de rayonnement durant la formation de deux radiographies pour un affichage stéréoscopique. Les informations sont acquises sur des régions des deux radiographies, qui doivent être élargies et qui correspondent l'une à l'autre. Des radiographies élargies, qui sont des élargissements des régions devant être élargies, sont produites à partir de chacune des deux radiographies. Sur la base des informations d'état d'imagerie, des positions se correspondant mutuellement sur les deux radiographies ‑ qui correspondent à la position de la surface la plus antérieure du sujet vue depuis la source de rayonnement ‑ sont spécifiées. Sur la base des positions spécifiées, les positions d'affichage pour les radiographies élargies sont déterminées de manière à ce que les positions de la surface la plus antérieure de la région devant être élargie coïncident avec les positions de la surface la plus antérieure du sujet dans l'espace d'affichage stéréoscopique. Les deux radiographies élargies sont affichées aux positions d'affichage déterminées.
PCT/JP2012/000425 2011-01-27 2012-01-24 Procédé d'affichage d'image stéréoscopique, et programme et appareil de commande d'affichage d'image stéréoscopique WO2012102022A1 (fr)

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH03141932A (ja) * 1989-10-30 1991-06-17 Toshiba Corp ステレオ視観察のためのｘ線画像取得表示方法及びその装置
JPH1051813A (ja) * 1996-07-29 1998-02-20 Toshiba Corp Ｘ線ステレオ画像表示装置
JP2005349127A (ja) * 2004-06-14 2005-12-22 Canon Inc 立体画像生成システムおよびその制御方法
JP2007531554A (ja) * 2003-11-03 2007-11-08 ブラッコ イメージング エス．ピー．エー． 管状構造を立体的に表示するディスプレイ及び該ディスプレイのための改善された技術（「ステレオ・ディスプレイ」）
JP2010187916A (ja) * 2009-02-18 2010-09-02 Fujifilm Corp 画像処理装置、画像処理システム及びプログラム

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH03141932A (ja) * 1989-10-30 1991-06-17 Toshiba Corp ステレオ視観察のためのｘ線画像取得表示方法及びその装置
JPH1051813A (ja) * 1996-07-29 1998-02-20 Toshiba Corp Ｘ線ステレオ画像表示装置
JP2007531554A (ja) * 2003-11-03 2007-11-08 ブラッコ イメージング エス．ピー．エー． 管状構造を立体的に表示するディスプレイ及び該ディスプレイのための改善された技術（「ステレオ・ディスプレイ」）
JP2005349127A (ja) * 2004-06-14 2005-12-22 Canon Inc 立体画像生成システムおよびその制御方法
JP2010187916A (ja) * 2009-02-18 2010-09-02 Fujifilm Corp 画像処理装置、画像処理システム及びプログラム

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