JP2006314774A - Radiography apparatus with scout view function - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiography apparatus with a small sensor for obtaining scout view capable of positioning an area of interest for linear tomography, panoramic tomography, or CT imaging, which realizes less cost and prevents radiation exposure. <P>SOLUTION: The radiography apparatus comprises an X-ray generator 11 to generate X-rays by selective switching of an X-ray slit beam B and an X-ray broad beam BB, a first X-ray image sensor 12a that is longer than is wide and short in width, and a second X-ray image sensor 12b, which displays a scout view image generated by using the X-ray slit beam B and the first X-ray image sensor 12a. Selecting a requested area of interest (s) on the scout view image, and also selecting an image classification enable the X-ray generator 11, and the first X-ray image sensor 12a and the second X-ray image sensor 12b to synchronously move along an imaging track in response to the selected image classification for radiography. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an improvement in an X-ray imaging apparatus that sets a region of interest for a subject and captures a tomographic image of the region of interest.

  Recently, as an X-ray detector for measuring an X-ray to obtain an X-ray image, a two-dimensional image sensor having a short light receiving portion close to a square and a line type having a longer light receiving portion. Two types of image sensors are available.

  Many of the former digital X-ray imaging apparatuses using a two-dimensional image sensor are configured to use the image sensor as an alternative to a conventional X film, and such X-ray imaging apparatuses are already known. The imaging principle of various transmitted images and tomographic plane images is used.

  On the other hand, a digital X-ray imaging apparatus using the latter line-type image sensor irradiates a subject with an X-ray slit beam according to a predetermined imaging trajectory, and tracks the X-rays transmitted through the subject with a line-type image sensor. Then, after taking a number of strip-shaped X-ray images, the X-ray images are connected and arranged in time series to obtain a single X-ray image.

  Patent Documents 1 and 2 below disclose an X-ray imaging apparatus that performs panoramic X-ray imaging using a line-type image sensor.

  That is, Patent Document 1 discloses one that can freely select panoramic X-ray imaging using a film cassette and panoramic X-ray imaging using a digital sensor cassette. The digital sensor cassette includes a line-type image sensor. Is being used.

  In Patent Document 2, an electric X-ray image detector, which is a line-type image sensor, is disposed on the inner surface of an X-ray light receiving unit provided in the center of the front surface of the cassette housing, and a control signal corresponding to the turning of the turning arm. Is configured to be able to output an image signal necessary for generating a panoramic X-ray image in the form of a digital signal by electrically controlling the X-ray into an electric signal.

In Patent Document 3, a patient frame that holds and fixes a patient's head can be freely moved up and down, and a relative position displacement with respect to a turning arm that turns around the patient frame can be performed so that a desired part can be photographed. A medical X-ray imaging apparatus is disclosed. As an X-ray image sensor, a MIS type has recently been developed (Patent Document 4).
Japanese Patent Laid-Open No. 11-104127 JP-A-11-104128 JP 7-275240 A Japanese Patent No. 3066944

  By the way, the two-dimensional type image sensor can be used very easily as a substitute for the conventional X-ray film because of its shape, but the acquisition price increases dramatically according to the size of the light receiving part. There is a problem and it is practically difficult to use a large size two-dimensional image sensor. Further, in tomographic imaging in which a subject is photographed and a tomographic image is generated from the photographed image, a large-size two-dimensional image sensor is used, and the subject is irradiated with an X-ray cone beam corresponding to the size. If this happens, there will also be a problem of exposure to the subject.

  On the other hand, especially in tomographic image capturing that generates tomographic images from a large number of images, comparison is made so that only unnecessary small parts near the region of interest of the subject are excluded from imaging. A configuration that uses a narrow X-ray cone beam and obtains an X-ray image with a two-dimensional image sensor having a size corresponding to the X-ray cone beam is advantageous in terms of cost and exposure.

  The present invention is a novel X-ray imaging apparatus that performs tomographic imaging using a relatively narrow cone beam after accurately specifying the position of a region of interest of a subject, particularly in order to deal with the problem of exposure. The purpose is to provide.

  In order to solve the above-mentioned problems, the X-ray imaging apparatus according to claim 1, which is the first invention, is an X-ray generator capable of selectively generating an X-ray slit beam and an X-ray wide-area beam, In order to capture an image of a subject by receiving an X-ray slit beam, a first X-ray image sensor that is vertically long and small in width and a second X-ray image that captures an image of the subject by receiving an X-ray wide-area beam An X-ray imaging apparatus including a sensor, wherein the display unit displays a scout view image of a subject generated using the X-ray slit beam and the first X-ray image sensor, and the display unit A desired region of interest is selected on the displayed scout view image, and an imaging type selection means for selecting an imaging type of a tomographic plane image prepared in advance for the region of interest, the X-ray generator, and the first Second X-ray image sensor The Rekato while synchronously moved along a photographing track according to the type of the selected captured by the imaging type selecting means, and an X-ray imaging control means for performing X-ray imaging.

  The X-ray imaging apparatus according to claim 2 is characterized in that, in claim 1, the tomographic plane imaging type includes at least one of a linear tomographic plane image, a panoramic tomographic plane image, and an X-ray CT image. To do.

  According to a third aspect of the present invention, there is provided an X-ray imaging apparatus according to the first aspect, in which a scout view image of a subject generated using the second X-ray image sensor is displayed, and a scout view displayed on the display unit. A desired region of interest is selected on the image, and an imaging type selection means for selecting an imaging type of a tomographic plane image prepared in advance for the region of interest, the X-ray generator, the first image sensor, and the first image sensor X-ray imaging control means for performing X-ray imaging while synchronously moving any one of the two image sensors along the imaging trajectory corresponding to the imaging type selected by the imaging type selection means. Yes.

  According to a fourth aspect of the present invention, there is provided an X-ray imaging apparatus which captures an object by receiving an X-ray slit beam and an X-ray generator capable of generating either an X-ray slit beam or an X-ray wide-area beam. An X-ray imaging apparatus comprising an X-ray image sensor that receives an X-ray wide-area beam and images a subject, wherein the X-ray slit beam or the X-ray wide-area beam and the X-ray A display unit for displaying a scout view image of a subject generated using an image sensor, a desired region of interest on the scout view image displayed on the display unit, and a tomography prepared in advance for the region of interest The imaging type selection means for selecting the imaging type of the plane image, the X-ray generator, and the X-ray image sensor are synchronized along the imaging trajectory corresponding to the imaging type selected by the imaging type selection means. While moving in, and an X-ray imaging control means for performing X-ray imaging.

  According to a fifth aspect of the present invention, in any one of the third and fourth aspects, the scout view image includes a scan transmission image of a subject.

  According to a sixth aspect of the present invention, in any one of the third to fifth aspects, the scout view image includes a panoramic tomographic plane image or two-way simple radiography.

  According to a seventh aspect of the present invention, in any one of the third to sixth aspects, the tomographic plane image type includes at least one of a linear tomographic plane image, a panoramic tomographic plane image, and an X-ray CT image. It is characterized by that.

  The X-ray imaging apparatus according to claim 8, which is a third aspect of the invention, is configured to turn an X-ray generator and an X-ray detection unit supported by a support unit so as to face each other relative to a subject held by a holding unit. A medical X-ray imaging apparatus that includes a moving unit that operates and operates the moving unit to capture an X-ray image of a subject. The medical X-ray imaging apparatus includes an irradiation field control unit, and the X-ray tube is irradiated by the irradiation field control unit. An X-ray generator capable of selectively switching between an X-ray slit beam and an X-ray wide-area beam by controlling the shape of the line cone beam, and a panoramic tomography of the subject receiving the X-ray slit beam In order to capture a plane image, the first X-ray image sensor that is vertically long and small in width and the second X-ray image sensor that receives an X-ray wide-area beam and captures an X-ray CT image of the subject are provided. An X-ray detector comprising a X-ray detector; A display unit that displays a panoramic tomographic image of a subject generated using the beam and the first X-ray image sensor as a scout view image, and a desired region of interest on the scout view image displayed on the display unit In order to acquire an X-ray CT image of the selected region of interest selected by the second X-ray image sensor, a control unit that performs position control of the support unit and / or the holding unit is provided.

  An X-ray imaging apparatus according to a ninth aspect of the present invention is the X-ray imaging apparatus according to the eighth aspect, wherein the position control of the support portion and / or the holding means is on a plane that intersects with an axis that rotates the X-ray generator and the X-ray detection portion. It is characterized by two-dimensional control in two specified directions.

  An X-ray imaging apparatus according to a tenth aspect is the X-ray imaging apparatus according to the eighth aspect, wherein the position control of the support part and / or the holding means is on a plane intersecting with an axis for turning the X-ray generator and the X-ray detection part. It is characterized by three-dimensional control in two directions defined and one direction parallel to this axis.

  An X-ray imaging apparatus according to an eleventh aspect is the X-ray imaging apparatus according to any one of the eighth to tenth aspects, wherein the second X-ray image sensor is offset forward or backward in the turning direction of the X-ray detection unit, and the selected region of interest is displayed. X-ray CT imaging of the region of interest is performed by always projecting at a predetermined ratio or more.

The X-ray imaging apparatus according to claim 12 is the X-ray imaging sensor according to any one of claims 1 to 11, wherein the X-ray image sensor includes an X-ray image intensifier, a MOS sensor, a CMOS sensor, a TFT sensor, a CCD sensor, a MIS type sensor, An X-ray solid-state imaging device is used.

  Claims 1, 2, 3, and 12 select a desired region of interest on a scout view image of a subject generated by using an X-ray slit beam and a first X-ray image sensor that is vertically long and small in width. I am doing so. The scout view image here is a preliminary image photographing in which about one or two images are photographed with respect to the subject, but this scout view image is an X-ray such as a scanning type photographing or a panoramic tomographic image photographing. This is obtained by the slit beam, and the amount of exposure to the subject is reduced. Further, as the first X-ray image sensor, a relatively low-price line-type image sensor can be used, and the tomographic plane image only needs to be captured in a narrow range around the region of interest. As the X-ray image sensor, a two-dimensional image sensor having a small light receiving portion can be used. Therefore, it is advantageous in terms of cost.

  Particularly, in claim 3, the scout view image of the subject is generated and displayed using the second X-ray image sensor, and the second image sensor further functions as a sensor for acquiring the scout view image. Therefore, the second image sensor can be effectively used.

  A fourth aspect of the present invention and the subordinate claims 5 to 7, and 12 are configurations using a two-dimensional image sensor corresponding to an X-ray wide-area beam, and either an X-ray slit beam or an X-ray wide-area beam is used. In addition, a desired region of interest is selected on a scout view image of a subject generated using such an X-ray image sensor. Accordingly, when the scout view image is wide, it is not advantageous in terms of cost as compared with the configurations of claims 1 to 3. However, in the tomography of the region of interest, the irradiation width of the X-ray wide-area beam is restricted. Thus, the amount of exposure to the subject can be reduced. Further, if the width or height of the detection surface of the image sensor is limited to the width of the region of interest, there is no need for a large image sensor that can shoot an area other than the region of interest of the subject, and the irradiation field of the X-ray cone beam. Can be limited to a size corresponding to this image sensor.

  In claim 8 and claims 9 to 12 dependent thereon, a desired scout view image of an object generated using an X-ray slit beam and a first X-ray image sensor that is vertically long and small in width is desired. The region of interest is selected. The scout view image here is a preliminary image photographing in which about one or two images are photographed with respect to the subject, but this scout view image is an X-ray such as a scanning type photographing or a panoramic tomographic image photographing. This is obtained by the slit beam, and the amount of exposure to the subject is reduced. Further, as the first X-ray image sensor, a relatively low-price line-type image sensor can be used, and the tomographic plane image only needs to be captured in a narrow range around the region of interest. As the X-ray image sensor, a two-dimensional image sensor having a small light receiving portion can be used. Therefore, it is advantageous in terms of cost.

  In particular, since the position control of the support means and the subject holding means is two-dimensional control on the plane intersecting the turning axis, a known technique such as an XY table can be used, and the control becomes easy.

  In particular, since the position control of the support means and the subject holding means is three-dimensional control in two directions on the plane intersecting the turning axis and in one direction parallel to this axis, a known XY table or the like is known. Technology can be used and control becomes easy.

  In particular, since the region of interest is partially projected on the second imaging means, X-ray CT imaging of a region of interest larger than normal X-ray CT imaging can be performed.

  Hereinafter, an example of an X-ray imaging apparatus having a scout view function according to the present invention will be described with reference to the drawings.

FIG. 1 is a block diagram illustrating a schematic configuration of an example X-ray imaging apparatus M.
FIG. 2 is a schematic diagram for explaining the mechanism of the X-ray generator 11 used in the X-ray imaging apparatus M. FIG. 3 is an external view for explaining an example of the basic configuration of the X-ray detector 12.

  As shown in FIG. 1, the X-ray imaging apparatus M includes an X-ray generator 11 that faces each other with a subject o interposed therebetween, and a moving unit 13 that includes an X-ray detector 12 having an X-ray detector 12c. The X-ray generator 11, the X-ray detector 12, and the X-ray imaging control means 14 for controlling the moving means 13 are configured.

  The X-ray generator 11 is an X-ray tube 11a that generates X-rays by tube current or tube voltage controlled by the X-ray imaging control means 14, and a collimator (not shown) for extracting X-rays emitted from the X-ray tube 11a. And primary slit plates 11b and 11b for restricting the X-ray irradiation range. Here, the X-ray tube 11a constitutes an X-ray source, and the collimator and the primary slit plates 11b and 11b constitute an irradiation field control means 11D.

  The primary slit plate 11b shown in FIG. 2A is vertically long (about 5: 1 to 100: 1, preferably 10: 1 to 50: 1, more preferably 15: 1) to the X-ray shielding plate. ˜30: 1) is formed, and the X-ray generated in the X-ray tube 11a is restricted in the irradiation range by the narrow groove 11c, and is long and narrow. The gap beam B is irradiated toward the subject o. The shape of the irradiation field perpendicular to the traveling direction of the X-ray slit beam may be any shape, such as a rectangle, an ellipse, or a rectangle with rounded corners. By changing the shape of the narrow groove 11c, realizable.

On the other hand, the primary slit plate 11b shown in FIG. 2B has a rectangular gap 11d (an aspect ratio of 1: 0.5 to 1: 1.5, preferably 1: 0) that is close to a square by an X-ray shielding plate. X-rays generated in the X-ray tube 11a are limited in the irradiation range by the rectangular gap 11d and have a predetermined spread. As shown in FIG.

An X-ray cone beam can be used as the X-ray wide-area beam. The shape of the irradiation field perpendicular to the traveling direction of the X-ray wide-area beam may be any shape, such as a circle, an ellipse, a square, and an octagon. That is, the X-ray wide-area beam can have various shapes such as a cone, a quadrangular pyramid, and an octagonal pyramid.
This can be realized by changing the shape of the rectangular gap 11d.

  Therefore, in the X-ray generator 11 adopting the irradiation field control means 11D comprising the primary slit plate 11b shown in FIGS. 2A and 2B, the X-ray imaging control means 14 causes the irradiation field control means 11D to be changed. By controlling one of the two primary slit plates 11b and 11b shown in FIGS. 2 (a) and 2 (b), the X-ray slit beam B or X-ray corresponding to the selected gap is selected. A wide beam BB can be selectively switched and generated.

  In addition, the primary slit plate 11b shown in FIG. 2C is obtained by forming both the narrow groove-shaped gap 11c and the rectangular gap 11d on a single X-ray shielding plate. In the X-ray generator 11 that employs the irradiation field control means 11D composed of the slit plate 11b, the X-ray imaging control means 14 drives an actuator (not shown) of the irradiation field control means 11D and the like of the X-ray tube 11a. By sliding the primary slit plate 11b arranged in the forward direction to the left and right, the X-ray slit beam B or the X-ray wide-area beam BB can be selectively switched and generated.

  The X-ray detector 12 has a configuration in which the X-ray detector 12c is incorporated, or a configuration in which a cassette as the X-ray detector 12c is detachably attached. The X-ray detector 12c is an X-ray image sensor, A first image sensor 12a and a second image sensor 12b corresponding to the X-ray slit beam B and the X-ray wide-area beam BB irradiated by the X-ray generator 11 are provided. The first image sensor 12a is a CCD image sensor having a vertically long light receiving portion corresponding to the X-ray slit beam B, and the second image sensor 12b is a two-dimensional light having a rectangular light receiving portion corresponding to the X-ray wide-area beam BB. A CMOS image sensor of the type is preferable. However, the present invention is not limited to this, and both may be a CCD image sensor or a CMOS image sensor.

  That is, in the present invention, the configuration of the X-ray image sensor is not limited, and the first and second image sensors 12a and 12b are CCD sensors, MOS sensors, CMOS sensors, TFT sensors, FT sensors, X-rays, or the like. It is configured by any one of a solid-state imaging device, XII (X-ray image intensifier), and MIS type sensor. Note that the MIS sensor means a metal insulator semiconductor sensor described in Patent Document 4 having a structure including a metal, an insulating layer, and a semiconductor layer.

In the above description, a rectangular light receiving unit sensor is used as the second image sensor. However, the second image sensor is not limited to this, and is basically a two-dimensional image sensor having a spread corresponding to the X-ray wide-area beam BB. There may be various shapes such as a circle, an ellipse, and an octagon.

  In the X-ray detector 12c shown in FIG. 3A, a first image sensor 12a and a second image sensor 12b are provided on each of two opposing surfaces of a rectangular housing. The X-ray imaging control means 14 drives an actuator or the like (not shown) and rotates the housing horizontally 180 degrees to select either the first image sensor 12a or the second image sensor 12b. Then, it faces the X-ray generator 11.

  In the X-ray detector 12c shown in FIG. 3B, a first image sensor 12a and a second image sensor 12b are both provided on one side surface of a rectangular housing. By driving an actuator or the like (not shown) by the imaging control means 14 and sliding the housing horizontally, either the first image sensor 12a or the second image sensor 12b is selected and X-rays are selected. It faces the generator 11.

  In FIG. 3C, the X-ray detection unit 12 is composed of a cassette holder 12i similar to the cassette holder of a panoramic imaging apparatus on which a conventional film cassette is mounted, and an X-ray detector 12c detachably attached to the cassette holder 12i. It is an example. Both the first image sensor 12a and the second image sensor 12b are provided on the side surface of the X-ray detector 12c, and the cassette holder 12i rotates in a groove 12h formed in the upper longitudinal direction thereof. It can be displaced in the horizontal direction across the X-ray irradiation direction with respect to the support portion 12a by a feed motor 12f fixed to the support portion 12a to be described later in contact with the shaft 12f1. This horizontal displacement can be used for the offset of the second image sensor described later.

  FIG. 25 shows an example of the shape of the detection surface S1 of the first image sensor 12a and the detection surface S2 of the second image sensor 12b. The example of FIG. 25A is an example in which the detection surface S1 and the detection surface S2 are rectangular or rectangular, but for example, a shape with rounded corners as shown in FIG. 25B may be used. is there.

  Here, the maximum vertical dimension of the detection surface S1 is W1f, the maximum vertical dimension of the detection surface S2 is W1g, the maximum horizontal dimension of the detection surface S1 is W2f, and the maximum horizontal dimension of the detection surface S2 is W1f. If the significant dimension is W2g, it can be set so that W1f> W1g and W2f <W2g. These vertical and horizontal dimensions can also be set from a ratio, and may be set to have a relationship of W1f / W2f> W1g / W2g. For example, if W2f is 1, W1f may be set at a ratio of 3-30, and if W2g is 1, W1g may be set at a ratio of 0.3-2.

  More specifically, W1f is conventionally set to about 150 mm or 150 mm ± 30 mm, which is most suitable for panoramic tomographic plane images, and W2f is set to about 10 mm or about 10 mm ± 5 mm, which is also suitable for clear imaging of the target tomography. W1g is about 120 mm or 120 mm ± 30 mm suitable for imaging only several dentitions or ear stapes, and W2g is also used to image only several dentitions or ear stapes. It may be set to about 120 mm or 120 mm ± 30 mm suitable for.

  By setting the slit, the shape of the irradiation field of the X-ray slit beam on the detection surface S1 is formed into a shape suitable for the detection surface S1, and the irradiation field of the X-ray wide-area beam on the detection surface S2 is formed. If the shape is formed in a shape suitable for the detection surface S2, the X-ray beam can be irradiated without waste.

The second image sensor 12b may be modified to employ an image sensor such as the image sensor 12b ′ in FIG. Both the detection surface S1 and the detection surface S2 are set in the image sensor 12b ′. In the image sensor 12b ′, the vertical maximum width dimension is set to the vertical maximum width dimension W1f of the detection surface S1, and the horizontal maximum width dimension is set to the horizontal maximum width dimension of the detection surface S2. Is set.

  Therefore, both the detection surface S1 and the detection surface S2 can be set on the middle imaging surface of the same image sensor 12b ′. When this image sensor is employed, the first image sensor 12a and the second image sensor 12b can be configured by the same image sensor 12b ′.

A modification of the X-ray detector 12c shown in FIG. 3C using the image sensor 12b ′ is an X-ray detector 12c shown in FIG.
In the X-ray detector 12c of FIG. 25D, the first image sensor 12a and the second image sensor 12b of the X-ray detector 12c of FIG. 3C are configured by the same image sensor 12b ′. ing.

  That is, the image sensor 12b ′ is an X-ray image sensor that receives an X-ray slit beam to capture an image of a subject, and is used as an image sensor that receives an X-ray wide-area beam and captures an image of the subject. Can do.

  The horizontal width W2g of the image sensor 12b ′ cannot capture the entire head or dentition of the patient as a subject at a time, for example. However, the vertical width is sufficient to be used for panoramic tomographic image capturing, for example. Set to the correct dimensions. In addition, regarding the small dimension of the horizontal width W2g, it is also possible to synthesize a wide range of images by displacing the support portion 13a in the horizontal direction and changing the position, and shooting a plurality of times.

  Note that the horizontal width of all the second image sensors 12b of the present invention is set to a region of interest s required in a specific medical field such as dentistry and otolaryngology (for example, only the dental arch or a specific part in the dental row). And the size of the irradiation field of the wide-area beam BB irradiated to the second image sensor 12b is also set to the second width of the second image sensor 12b. If the size of the image sensor 12b is set to a necessary size, it is possible to irradiate a wide-area beam toward only the region of interest, thereby reducing the amount of exposure.

  Similarly, the vertical width of the second image sensor 12b is set to a size corresponding to the vertical width of the region of interest s, and the irradiation field of the wide-area beam BB irradiated to the second image sensor 12b is large. Alternatively, the size may be set as much as necessary for the second image sensor 12b.

  The moving means 13 holds the support portion 13a having the X-ray generator 11 and the X-ray detection portion 12, and the rotation axis A of the support portion 13a so as to freely rotate and hold the rotation axis A. An axis moving table 13b that can move the axis A along a horizontal plane and a holding means 13c that positions the subject o are configured. For the turning movement of the support part 13a and the horizontal movement of the rotation axis of the support part 13a, independent stepping motors controlled by the X-ray imaging control means 14 are used as drive sources. Further, the holding means 13c may be moved up and down by a similar stepping motor.

  The irradiation angle of the X fine slit beam B or the X-ray wide-area beam BB is basically parallel to the horizontal plane, but is not limited to this. That is, a configuration in which the subject o is irradiated with X-rays at an oblique irradiation angle with respect to the horizontal plane is also conceivable. This is because metal parts such as dentures have a large artifact in X-ray photography, and there are cases where it is desired to take pictures while avoiding metal parts. This is a problem particularly in X-ray CT image capturing. Therefore, in that case, it is desirable to irradiate the subject o with the X-fine slit beam B or the X-ray wide-area beam BB so as to avoid the metal portion.

  The X-ray imaging control unit 14 includes a motor control unit 13d having a stepping motor that drives the moving unit 13, a display unit 15a that displays information such as an X-ray image on a monitor television, and an operation unit that receives operations such as a keyboard and a mouse. 15b etc. are connected, and as a functional element, the tube current and tube voltage of the X-ray tube 11a of the X-ray generator 11 are controlled, and further, the primary slit plate 11b of the irradiation field control means 11D is operated, X-ray generation control means 14a for selectively switching between the X-ray slit beam B and the X-ray wide-area beam BB and either the first image sensor 12a or the second image sensor 12b generate X-rays. The image sensor control means 14b that acquires the data of the X-ray image transmitted through the object o and the motor control unit 13d is operated by moving it in a state where it faces the device 11, and is moved by controlling the motor control unit 13d. An imaging trajectory control means 14c for operating the means 13 to move the X-ray generator 11 and the X-ray detector 12 along an imaging trajectory corresponding to the type of imaging, and a transmission image from the acquired X-ray image data And image generation means 14d for generating a tomographic image.

  The display unit 15a and the operation unit 15b display, as a wide range image of the subject o, that is, a scout view image, an image taken prior to the target tomography, and a tomographic plane or diagnosis to be tomographed inside the subject o The region of interest s, which is a part, is selected, and the imaging type selection means 15 for selecting the imaging type of the tomographic image for the region of interest s is configured. Here, the scout view image is used for preliminary photographing or preliminary diagnosis.

  Next, imaging of a scout view image, selection of an imaging type, and imaging of a tomographic plane image which are basic operations of the X-ray imaging apparatus M will be described in order.

  In capturing a scout view image, the X-ray generator 11 and the X-ray detector 12 are synchronously moved along a predetermined imaging trajectory, and the subject o is irradiated with the X-ray slit beam B. The feature is to obtain an image. Further, as such a scout view image, a linear scan transmission image, a panoramic tomographic plane image, or the like can be used, and the selection of an imaging type to be used is set in advance by the imaging type selection unit 15. It is supposed to keep.

  In any invention of the present application, there may be one or a plurality of imaging types of scout view images, and there may be one or a plurality of imaging types of tomographic image captured from the scout view.

  In addition to taking a scout view image with the first image sensor and taking a tomographic image with the second image sensor, the scout view image is taken with the second image sensor and the first image sensor. A tomographic image may be taken, or a scout view image may be taken by the first image sensor, and a tomographic image may be taken by the first image sensor.

Further, a scout view image may be taken with the second image sensor, and a tomographic plane image may be taken with the second image sensor. Further, these combinations may be duplicated, and this combination is free.

  That is, an example in which a scout view image is captured by the first image sensor and a tomographic plane image is captured by the second image sensor is, for example, a panoramic tomographic plane image, a cephalometric image, or a linear scan using the first image sensor. The transmission image is a scout view image, and an X-ray CT image is captured as a tomographic image using a second image sensor.

  An example in which a scout view image is captured by the second image sensor and a tomographic plane image is captured by the first image sensor is, for example, a simple captured image is used as a scout view image using the second image sensor, In this configuration, a panoramic tomographic plane image is captured as a tomographic plane image using one image sensor.

  An example in which a scout view image is captured by the first image sensor and a tomographic image is captured by the first image sensor is, for example, a linear scan transmission image or a cephalo image is used as the scout view image using the first image sensor. The panorama tomographic image is captured as a tomographic image using the first image sensor.

  An example of taking a scout view image with the second image sensor and taking a tomographic image with the second image sensor is, for example, using the second image sensor as a scout view image, In this configuration, an X-ray CT image or a linear tomographic image is captured as a tomographic image using an image sensor.

  An example of overlapping of these combinations is, for example, a case where a scout view image is taken with a first image sensor, and an example where a tomographic plane image is taken with a second image sensor is, for example, a panorama using a first image sensor. In a configuration in which a tomographic image, a cephalo image, or a linear scan transmission image is used as a scout view image, and an X-ray CT image is captured as a tomographic image using a second image sensor, simple imaging using a second image sensor is further performed. The image is a scout view image, and a panoramic tomographic image can be taken as a tomographic image using the first image sensor.

  Although it will be complicated, it will not be described in detail any more, but various combinations are possible in the scout view and tomographic image imaging of FIG.

  In this imaging, the imaging trajectory control means 14c reads the trajectory data stored in an imaging trajectory memory (not shown), and controls the moving means 13 through the motor control unit 13d, whereby the X-ray generator 11 and the X-ray detection are detected. The unit 12 is moved synchronously along the imaging trajectory defined by the read trajectory data. The X-ray generation control means 14a irradiates the subject o with the X-ray slit beam B from the X-ray generator 11 according to intensity data stored in an irradiation intensity memory (not shown), that is, a profile. On the other hand, the image sensor control unit 14b measures the X-rays transmitted through the subject o by the first image sensor 12a and transmits the data to the image generation unit 14d. When this shooting is completed, the image generation unit 14d can generate a scout view image by arranging a series of transmitted data in time series. The profile may be selected according to the sex or physique of the subject who is the subject o, or the X-ray intensity measured by the first image sensor 12a is fed back and controlled regardless of the profile. You may do it.

  In the selection of the photographing type, a linear scan transmission image, a panoramic tomographic image, and the like photographed as a scout view image are displayed on the display unit 15a together with a movable cursor on the image. The region of interest s can be determined by an operation such as mouse click after the cursor is moved to the region of interest s such as a tomographic plane or a diagnostic region. Then, when an imaging type of a tomographic image captured for the region of interest s is selected by an operation such as pressing a predetermined key, tomographic imaging is started. As the tomographic plane image, a linear tomographic plane image, an X-ray CT image, a panoramic tomographic plane image, or the like can be selected.

For tomographic plane imaging, for example, X-ray CT images and linear tomographic plane images can be captured while the X-ray generator 11 and the X-ray detector 12 are moved synchronously along a predetermined imaging trajectory. The X-ray generator 11 emits the X-ray wide-area beam BB, and the second image sensor 12b of the X-ray detector 12c takes a plurality of transmission images of the subject o as a frame image having a predetermined spread. After obtaining a plurality of transmission images corresponding to the position of the imaging trajectory, a tomographic plane image of the region of interest s is obtained by image processing that combines or calculates them.
Further, for example, in the case of photographing a panoramic tomographic plane image, a transmission image obtained by irradiating the X-ray slit beam B from the X-ray generator 11 toward the first image sensor is subjected to image processing by calculation, and panoramic tomography is performed. A surface image is obtained.

  In this imaging, the imaging trajectory control means 14c reads the trajectory data stored in an imaging trajectory memory (not shown), and controls the moving means 13 through the motor control section 13d, whereby the X-ray generator 11 and the X-ray detection section. 12 are moved synchronously along the imaging trajectory for tomographic image imaging defined by the read trajectory data. Further, when the X-ray generation control means 14a reaches the position of the predetermined imaging trajectory, the X-ray generation beam 11 is transmitted from the X-ray generator 11 according to the intensity data stored in the irradiation intensity memory (not shown), that is, the profile. The image sensor control unit 14b receives X-rays transmitted through the region of interest s by the second image sensor 12b and the first image sensor 12a, and generates a transmission image. It is made to transmit to the means 14d. When this imaging is completed, the image generation unit 14d can perform a predetermined process on the transmitted transmission image and generate a tomographic plane image of the region of interest s. Note that the profile may be selected according to the gender and physique of the subject who is the subject o, or the second image sensor 12b or the first image sensor 12a receives the light and measures regardless of the profile. The X-ray intensity may be fed back and controlled.

  Here, an imaging trajectory when capturing a linear scan transmission image or a panoramic tomographic plane image as a scout view image, and an example of an obtained image will be described with reference to the drawings.

  FIG. 4 shows that the X-ray generator 11 and the X-ray detector 12 move synchronously when taking a linear scan transmission image that synchronously moves the X-ray generator and the X-ray detector in the same direction as a scout view image. FIG. 5 is an example of a linear scan transmission image of the subject o obtained by the photographing, and is an image displayed in the selection of the photographing type. In this example, the lower jaw of a person is used as the subject o, and a cross-cursor cursor for designating the region of interest s is also drawn.

  In this case, the imaging trajectory control means 14c controls the X-ray generator 11 that is irradiated with the X-ray slit beam B by controlling the moving means 13, thereby imaging from the position (p1) to the position (p2). While moving along the trajectory, the first image sensor 12a of the X-ray detector 12c is moved synchronously along the imaging trajectory from the position (q1) to the position (q2). By photographing according to such a photographing trajectory, a front linear scan transmission image of the subject o as shown in FIG. 5A is obtained.

  Similarly, the first X-ray detector 12 of the X-ray detector 12 is moved while moving the X-ray generator 11 adapted to irradiate the X-ray slit beam B along the imaging trajectory from the position (p3) to the position (p4). The side linear scan transmission image of the subject o as shown in FIG. 5B can be obtained by photographing in which the image sensor 12a is moved synchronously along the photographing trajectory from the position (q3) to the position (q4). it can.

In FIG. 4, the apex side of the dental arch is directly above the figure, and the X-ray generator 11 moves from position (p1) to position (p2) from right to left in the figure, The first image sensor 12a is moved from the right to the left in the figure from the position (q1) to the position (q2).
In addition, the X-ray generator 11 moves from the top (down) to the bottom (p4) from the position (p3), and similarly, the first image sensor 12a moves from the position (q3) to the position (q4). It moves from top to bottom in the figure.

The linear scan transmission images of the front and side surfaces of the subject o photographed in this way are simultaneously displayed on the display unit 15a and used for setting the region of interest s of the subject o.
Acquisition of a scout view image from two different directions with respect to the subject o is referred to as “two-way scout”.

  The panoramic tomographic plane image referred to in the present application is a tomographic image of teeth and jaws along the dental arch, and a panoramic tomographic plane image of the subject o as shown in FIG. It is done.

  As shown in FIG. 24, the trajectory during panoramic tomographic image shooting is a substantially triangular shape that is subject to left and right with the vertex of the X-ray slit beam moving toward the front tooth portion of the dental arch as a boundary. It is possible to adopt a configuration of a known panoramic X-ray imaging apparatus that moves the X-ray detector and the X-ray generator so as to draw an envelope trajectory.

  FIG. 24 shows how the trajectory of the X-ray slit beam B irradiated from the X-ray generator 11 toward the first image sensor 12a draws an envelope EN. That is, the trajectory of the X-ray slit beam B becomes the envelope EN by the combination of the turning of the X-ray generator 11 and the first image sensor 12a by the turning of the support portion 13a and the movement of the turning axis A of the support portion 13a. Forming.

  FIG. 23 is an example in which a scout view image is obtained by the X-ray slit beam B using the second image sensor 12b. The basic configuration is the same as that in FIG. 4 except that the X-ray detection unit does not move during imaging and the second image sensor 12b is fixed for imaging. In FIG. 23, the front tooth side apex of the dental arch is directly above the figure, and the X-ray generator 11 moves from the position (p51) to the position (p52) from the right to the left in the figure. Getting a view. Of course, the above-described two-way scout can be acquired by this imaging method.

  When a scout view is acquired by the second image sensor 12b, a simple X-ray fluoroscopic image may be obtained using the X-ray wide-area beam BB (hereinafter referred to as “simple imaging”). ), And the configuration shown in FIG.

  The advantage of the configuration of FIG. 23 is that irradiation with only a limited area of the second image sensor 12b is also possible. For example, when a scout view is sufficient in the vicinity of one temporomandibular joint, only the vicinity of one temporomandibular joint can be irradiated. This imaging method is referred to as “scan X-ray imaging” in the present application.

  Furthermore, an example of an imaging trajectory when a linear tomographic image or an X-ray CT image is acquired as a tomographic image will be described with reference to the drawings. It is also possible to take a panoramic tomographic image as a tomographic image.

  In taking a linear tomographic plane image, the subject o is always irradiated with the X-ray wide-area beam BB with the projection angle changed around only the target predetermined tomographic plane, and only the predetermined tomographic plane is emphasized. As described above, a tomographic image is obtained by dispersing image information of X-rays transmitted through a part other than a predetermined tomographic plane. The linear tomographic plane referred to in the present application is the above-described predetermined tomographic plane that is photographed at the center. The imaging position includes a plurality of points with different projection angles on the imaging trajectory. It is also possible to take a linear tomographic image using the X-ray slit beam B.

  Further, X-ray CT imaging is performed by rotating the X-ray wide-area beam BB at an angle of at least 180 or more around the region of interest s so that the region of interest s set on the subject o is always included. A tomographic plane image in an arbitrary direction is obtained by calculating a back projection image for a large number of transmission images photographed for each predetermined turning angle.

  The panoramic tomographic image is captured in such a manner that the X-ray slit beam B is vertically irradiated toward the dental arch which is the region of interest s set on the subject o and the dental arch is subdivided. The images are sequentially overlapped or synthesized to obtain a single panoramic tomographic image, but microscopically, images taken from different angles are superimposed or synthesized. That is, in the panoramic tomographic plane image, the images acquired with the X-ray slit beam are sequentially superimposed or synthesized so that the cross section of the dental arch is emphasized.

  FIG. 8A is a plan view illustrating an imaging trajectory in which the X-ray generator 11 and the X-ray detector 12 move synchronously when imaging a linear tomographic image as a tomographic image. Here, a tomographic plane is set as the region of interest s for the subject o. FIG. 8B is different from FIG. 8A in the trajectory in which the X-ray generator 11 and the X-ray detector 12 move. That is, in the locus of FIG. 8A, the X-ray generator 11 and the X-ray detector 12c linearly move in opposite directions with respect to a predetermined predetermined tomographic plane indicated by the region of interest s in the figure. On the other hand, the X-ray generator 11 and the X-ray detector 12c are circularly moved in directions opposite to each other along the locus of FIG.

  In this case, the imaging trajectory control means 14c controls the X-ray generator 11 that irradiates the X-ray wide-area beam BB by controlling the moving means 13 so that the imaging trajectory heads from the position (p31) to the position (p33). The second image sensor 12b of the X-ray detector 12c is moved synchronously along the imaging trajectory from the position (q31) to the position (q33). A linear tomographic plane image can be synthesized by photographing according to such a photographing trajectory.

  For example, during imaging in accordance with the imaging trajectory, a transmission image can be sequentially acquired as a unit frame image, and the frame images can be combined with a linear tomographic image by superimposing only a desired tomographic part.

In addition, for example, one linear tomographic image in which image data is accumulated as a single image can be acquired without obtaining a transmission image divided into a plurality of images during imaging according to the imaging trajectory. . This is based on the same principle as the conventional film photographing in which only the information on a specific linear tomographic plane is accumulated and emphasized because information is dispersed in portions other than the target linear tomographic plane.

  FIG. 9 is a plan view illustrating an imaging trajectory in which the X-ray generator 11 and the X-ray detection unit 12 move synchronously when an X-ray CT image is acquired as a tomographic plane image. Here, in the subject o, a cylindrical diagnostic region is set as the region of interest s.

In this case, the imaging trajectory control means 14c controls the X-ray generator 11 adapted to irradiate the wide X-ray beam BB by controlling the moving means 13 so that the imaging trajectory heads from the position (p41) to the position (p43). The second image sensor 12b of the X-ray detector 12c is moved synchronously along the imaging trajectory from the position (q41) to the position (q43).
The X-ray generator 11 moves from the position (p41) toward the position (p43), and the first image sensor 12a moves from the position (q41) toward the position (q43). The center of rotation with the image sensor 12b is rotated in a circle in a region of interest s.
The turning angle required for X-ray CT imaging is at least 180 °.

  A tomographic plane image can be synthesized for an arbitrary cross section of the region of interest s by back-projecting a transmission image obtained by imaging according to such an imaging trajectory by a known method.

  Here, a series of operations including imaging of the scout view image, selection of the imaging type, and imaging of the tomographic plane image are shown as flowcharts in FIGS.

  FIG. 10 shows a procedure in which a linear scan transmission image in two directions is captured as the scout view image (two-way scout described above), a linear tomographic image is selected by selecting the imaging type, and the tomographic image is captured. It is a flowchart.

  Here, in steps 101 and 102, linear scan transmission images in two directions are taken, in steps 103 to 106, a region of interest is selected, and a linear tomographic plane image is selected as a tomographic plane image. In steps 107 to 108, The tomographic image is taken.

  FIG. 11 is a flowchart showing a procedure when a panoramic tomographic plane image is captured as a scout view image, a linear tomographic plane image is selected by selecting an imaging type, and the tomographic plane image is captured.

  Here, panoramic tomographic plane images are taken in steps 201 and 202, a region of interest is selected in steps 203 to 206, and a linear tomographic plane image is selected as a tomographic plane image. In steps 207 to 208, the tomographic plane image is selected. A plane image is being taken.

  The above is a case where a linear tomographic image is captured from a scout view image in FIGS. 10 and 11, but the CT mode may be selected as shown in FIGS. 20 and 21. It is possible to select the linear tomographic mode in steps 106 and 206 or the CT mode in steps 506 and 606. In steps 507 and 607, the apparatus is arranged so that the notified coordinate point is at the center of the X-ray CT image. Has moved.

  When proceeding to the linear tomographic mode, linear tomographic plane image capturing at steps 108 and 208 is performed, and when proceeding to the CT mode, capturing of X-ray CT images at steps 508 and 608 is performed.

  Both the above-described linear tomographic image capturing and X-ray CT image capturing can be performed by the second image sensor 12b of the X-ray detector 12c, and thus a plurality of types of tomographic image capturing can be performed.

  FIG. 22 is a table summarizing the combinations of what kind of tomographic images can be taken from what kind of scout view.

  FIG. 12 is a flowchart showing a procedure in the case of taking a linear scan transmission image in one direction as a scout view image (one-way scout), selecting a panoramic tomographic plane image by selecting an imaging type, and capturing the tomographic plane image. is there.

  Here, in steps 301 and 302, a linear scan transmission image in one direction is taken, in steps 203 to 306, a region of interest is selected, and further, a panoramic tomographic plane image is selected as a tomographic plane image, and in steps 307 to 308, The tomographic image is taken.

Next, a more specific example of the X-ray imaging apparatus M according to the present invention will be described with reference to the drawings.
FIG. 13 is a perspective view of the X-ray imaging apparatus M, and FIGS. 14 and 15 are a plan view and a side view of an example in which a cephalo image imaging means 18 is further added.

  The digital X-ray tomography apparatus M includes a moving means 13 having an X-ray generator 11 and an X-ray detector 12 and a main body frame 16 that firmly supports the moving means 13.

  The moving means 13 includes a support portion 13a to which the X-ray generator 11 and the X-ray detector 12 are fixed, and a rotation axis A in the Z direction on a plane XY perpendicular to the rotation axis A of the support portion 13a. And a shaft moving table 13b for horizontally moving the shaft. This axis moving table 13b is an axis moving mechanism that can freely move in the XY plane by a motor controller 13d having a stepping motor that drives the mechanism of the moving means 13, an X-axis stepping motor, and a Y-axis stepping motor. The rotating shaft connected to the shaft slide portion can be moved horizontally, and the support portion 13a can be swung freely by the rotating shaft stepping motor. The moving means 13 can also move up and down along the main body frame 16 by a Z-axis stepping motor.

  However, since the patient who is the subject o can be in a standing position or a supine position, the rotation axis direction of the support portion 13a is not limited to this example and may be arbitrary.

  The X-ray generator 11 is based on the basic configuration described with reference to FIG. 2, and includes an X-ray tube 11a having a fixed anode, a metal collimator, a narrow groove 11c for the X-ray slit beam B, and an X-ray wide area. It is composed of a primary slit plate 11b having a rectangular gap 11d for the beam BB, and selectively irradiates either the X-ray slit beam B or the X-ray wide-area beam BB. Here, the X-ray tube 11a constitutes an X-ray source, and the metal collimator and the primary slit plate 11b constitute an irradiation field control means 11D.

  FIG. 16 is an example of primary slit setting. When the cassette (type of imaging) is switched, or when the type of imaging is switched with the same cassette, the X-ray irradiation field shape irradiated from the X-ray generator 13 and the light-receiving shape on the X-ray detection unit 12 side are imaged. It is switched according to the form. An X-ray source X composed of an X-ray tube 11a is built in the housing including the X-ray generator 11, and the front surface of the housing facing the X-ray detector 12 has a primary slit SL1. A slit module SL including an adjustment mechanism for changing the shape of the line shielding plate and its primary slit is disposed. In the primary slit plate SL2 (corresponding to the primary slit plate 11b in FIG. 2) provided on the front side of the X-ray source X, as the primary slit SL1, a vertically long slit SL3 for panoramic tomographic plane imaging (FIG. 2). ), A rectangular slit SL4 for X-ray CT imaging (rectangular space 11d in FIG. 2), and a long cephalometric imaging slit SL5 (narrow groove-shaped space 11c in FIG. 2). If the cassette is changed, the slit module SL sets the primary slit SL1 corresponding to the cassette by the drive motor SM.

  The X-ray detector 12c that constitutes the X-ray detector 12 is based on the basic configuration described in FIG. 3, and is a fluorescent filter that converts X-rays into visible light, and an X-ray slit beam as the first image sensor 12a. A CCD image sensor having a vertically long light receiving portion corresponding to B, a CMOS image sensor having a short light receiving portion corresponding to the X-ray wide-area beam BB as the second image sensor 12b, and a secondary slit for shielding scattered X-rays It is configured as a cassette 12cc containing a plate or the like, and this cassette 12c is detachably attached to the cassette holder 12g. This cassette 12cc can be replaced with another cassette containing an X film.

  On the side surface of the housing frame 17 provided on the main body frame 16, there are provided a display unit 15a and an operation unit 15b composed of an indicator lamp and an operation switch, and further a control unit comprising a CPU or the like is stored therein. Yes. A holding means 13c for positioning the subject o is also attached to the housing frame 17.

  What is seen in the center when viewed from the front of the holding means 13c is a chin rest 13g on which the patient places his chin. The chin rest 13g can be moved up and down or tilted and positioned according to the patient's body shape. By configuring the chin rest 13g to be movable in this manner, for example, it is possible to adjust the inclination of the irradiation line with respect to the horizontal plane for each imaging region such as the upper jaw and the lower jaw, and the upper jaw joint and the lower jaw tip located below In this way, it is possible to adjust so that a site separated vertically is positioned in the center of the irradiation field.

Here, the structure of the moving means 13 and the accommodation frame 17 will be described in detail.
In the example of FIG. 13, the axis moving table 13b is displaced up and down with respect to the main body frame 16 in accordance with the patient's physique. The shaft moving table 13b and the housing frame 17 are integrally formed. Therefore, the X-ray generator 11 and the X-ray detector 12 are moved up and down together with the housing frame 17 and the holding means 13c.

  However, the housing frame 17, the X-ray generator 11, and the shaft moving table 13 b that accompanies the raising and lowering of the X-ray detector 12 are configured separately, and each is independently displaced with respect to the main body frame 16. It doesn't matter if you do. Moreover, you may comprise so that the X-ray generator 11 may be displaced with respect to the accommodating frame 17 thru | or the holding means 13d. The above-mentioned Patent Document 3 relating to the application of the present applicant describes an X-ray generator for an example in which the above-described housing frame 17 and the shaft moving base 13b are configured separately, or for the housing frame 17 or the holding means 13c. An example in which 11 is displaced is disclosed.

  In Patent Document 3, the portion corresponding to the housing frame 17 described above is referred to as a “patient frame”, and the portion corresponding to the axis moving table 13b is referred to as an “elevating body”. In addition, for example, by adjusting the tilt of the irradiation line with respect to the horizontal plane for each imaging region, the upper and lower jaw joints and the lower jaw tip located below can be irradiated well. It is to adjust so that it is located in the center of the field.

  The X-ray generator 11 is displaced with respect to the structure in which the chin rest 13g can be moved up and down or tilted, the structure in which the housing frame 17 and the shaft moving base 13b are separated, and the housing frame 17 or the holding means 13c. It may be possible to make finer adjustments by combining with the above-described configuration.

  This X-ray imaging control means 14 controls the tube current and tube voltage of the X-ray tube 11a of the X-ray generator 11 and operates the primary slit plate 11b to control the X-ray slit beam B. Or the X-ray generation control means 14a for selectively switching between the X-ray wide-area beam BB, the first image sensor 12a, and the second image sensor 12b are brought into contact with the X-ray generator 11. The image sensor control means 14b that acquires the data of the X-ray image transmitted through the subject o and the movement means 13 are operated by controlling the motor control section 13d, and the X-ray generator 11 is operated. The imaging trajectory control means 14c for moving the X-ray detection unit 12 along the imaging trajectory corresponding to the type of imaging, and the image generation means 14d for generating a transmission image and a tomographic plane image from the acquired X-ray image data. And To.

  The control unit can be connected to a display unit 15a for displaying information such as an X-ray image on a monitor television (not shown) and an operation unit 15b for receiving operations such as a keyboard and a mouse (not shown). The display unit 15a and the operation unit 15b display a wide range image of the subject o, that is, a scout view image, an image taken prior to the target tomography, and a tomographic plane to be tomographed inside the subject o Alternatively, an imaging type selection unit 15 that selects a region of interest s that is a diagnostic region and further selects an imaging type of a tomographic image for the region of interest s is configured.

  The cephalometric image capturing means 18 has the same configuration as the mounting arm portion 18a connected to the rear portion of the axis moving table 13b, the holding means 13c2 for positioning the subject o during cephalometric image capturing, and the X-ray detector 12c. Another X-ray detection unit 12A composed of a line detector is provided.

  At the time of cephalometric imaging, as shown in FIG. 14, the X-ray generator 11 is brought into a state where the X-ray generator 11 and another X-ray detector 12A made of an X-ray detector face each other. It is possible to shoot cephalo images using.

  In the X-ray imaging apparatus M shown in FIG. 1 as an embodiment, the X-ray generator 11 can selectively generate the X-ray slit beam B or the X-ray wide-area beam BB to generate X-ray detection. The X-ray detector 12c constituting the unit 12 receives the X-ray slit beam and captures an image of the subject o. Therefore, the X-ray detector 12c receives the first long image sensor 12a having a small width and the X-ray wide-area beam. A second image sensor 12b that captures an image of the subject o is used, and a scout view image of the subject o captured by the X-ray slit beam B and the first image sensor 12a is used to start from the subject o. The region of interest s is selected.

  However, the idea of the present invention is not limited to this, and the following modified configuration is possible. That is, an X-ray generator that can generate an X-ray wide-area beam BB and an X-ray image sensor that receives the X-ray wide-area beam BB and captures an image of the subject o, and these X-ray wide-area beam BB, It is also possible to select the region of interest s from the subject o using a scout view image of the subject o photographed by the X-ray image sensor (hereinafter referred to as simple photographing). Other components are common to the corresponding ones in the above-described embodiment. Further, with this modified configuration, the spread of the X-ray wide-area beam BB may be made different between when the scout view image of the subject o is captured and when the tomographic image of the region of interest s is captured.

  As specific examples that can be considered in various ways, the table in FIG. 22 is also described. For example, as a scout view image, a scout view image that is a linear scan transmission image from two directions, or a scout view image by simple photographing from two directions. May be used to perform linear tomographic image capturing or X-ray CT image capturing, and linear tomographic image capturing and X-ray CT image capturing may be selectable.

  Further, panoramic tomographic plane image capturing may be performed using a scout view image which is a linear scan transmission image from one direction or a scout view image obtained by simple imaging from one direction as a scout view image. Further, linear tomographic image capturing or X-ray CT image capturing may be performed using a scout view image that is a linear scan transmission image from two directions or a scout view image by simple imaging from two directions as a scout view image. .

  Using a scout view image that is a linear scan transmission image from two directions or a scout view image obtained by simple imaging from two directions as a scout view image, among panoramic tomographic image, linear tomographic image imaging, and X-ray CT image imaging From this, at least one tomographic image may be captured.

  In the above, it goes without saying that a configuration using a panoramic tomographic plane image as a scout view image may be added as appropriate. For acquisition of the scout view image, photographing by linear scanning and simple photographing may be used in a selectable manner.

  The following modified configuration is also possible. That is, an X-ray generator that can generate either the X-ray slit beam B or the X-ray wide-area beam BB, the subject o by receiving the X-ray slit beam B, and the X-ray wide-area beam received A scout view image of the subject o photographed by either the X-ray slit beam B or the X-ray wide-area beam BB and the X-ray image sensor. The region of interest s may be selected from the subject o. Other components are common to the corresponding ones in the above-described embodiment. In this configuration, an X-ray image sensor having a rectangular light receiving unit corresponding to the X-ray wide-area beam BB is used. When the subject o is imaged by receiving the X-ray slit beam B, one of the light receiving units is used. The part may be used. 25 (c) and 25 (d) described above are specific examples. Various possible embodiments are similar to those described above.

  In the present invention, the movement of the X-ray generator and the X-ray image sensor (X-ray detector or X-ray detector) with respect to the subject o is a relative movement. Therefore, the X-ray detector and the X-ray image sensor may be moved while the subject is fixed, or the X-ray detector and the X-ray image sensor may be fixed and the subject may be moved relative thereto. As described above, in the present invention, the movements of the X-ray generator and the X-ray image sensor with respect to the subject are all defined by the relative movement described above.

  For example, when it is necessary to rotate (rotate) the X-ray generator and the X-ray image sensor relative to the subject when taking a tomographic image, the subject is fixed and the X-ray generator and the X-ray image are fixed. The sensor may be rotated, but the subject may be rotated or moved while the X-ray generator and the X-ray image sensor are fixed. Further, rotation or movement of the subject may be combined with turning of the X-ray generator and the X-ray image sensor. The same applies to operations other than turning (rotation).

  The table shown in FIG. 22 shows combinations of tomographic image capturing from scout view images that are possible with the configuration of the present invention. The circles in this table indicate those that can be combined. The scout view image can be acquired as an image acquired by a vertically long X-ray image sensor and an image acquired by, for example, a rectangular two-dimensional image sensor having a spread corresponding to the X-ray wide-area beam BB.

  As the scout view image, images acquired by the first X-ray image sensor 12a which is vertically long and small in width include a linear scan transmission image, a panoramic tomographic plane image, and a cephalometric image, and a rectangular shape corresponding to an X-ray wide-area beam. An image acquired by a two-dimensional image sensor includes a simple photographed image, a panoramic tomographic plane image, and a cephalometric image. There is). In the case of the configuration of FIG. 23, a transmission image by the method of FIG. 23 is acquired by a two-dimensional image sensor. Further, the tomographic image imaging selected by the imaging type selection means includes panoramic tomographic image imaging, linear tomographic image imaging, and X-ray CT image imaging.

  The temporomandibular panoramic tomographic plane image can also be acquired using the whole jaw panoramic tomographic plane image as a scout view image.

  In this all-maxillary panoramic tomographic image photographing, the photographing is performed centering on the tomographic NP substantially along the center of the dental arch, as shown in FIG. Then, the image is taken centering on the tomogram JP around the temporomandibular joint.

In the present application, the term “panoramic tomographic plane image” refers to an entire jaw panoramic tomographic plane image without particular distinction.

  In a scout view based on a linear scan transmission image, which is an image acquired by a vertically long and narrow X-ray image sensor, a scout is used when acquiring a panoramic tomographic plane image as a target for tomographic plane image selection selected by the imaging type selection means. A linear scan image may be acquired for the view from only one direction with respect to the subject, or may be acquired from two directions.

  When acquiring from only one direction, specifically, acquiring from the side of the patient's head including the dental arch that is the subject is convenient for panoramic tomographic image capturing. This is because the position of the front teeth is important in panoramic tomographic image photography, and the position of the front teeth can be clearly grasped by acquiring from the side surface of the patient's head.

  An image acquired by a rectangular two-dimensional image sensor corresponding to an X-ray wide-area beam, and in a scout view based on a simple captured image, a panoramic tomographic plane image is obtained as an object of tomographic plane image selection selected by the imaging type selection means. At this time, a simple captured image may be acquired from only one direction with respect to the subject in the scout view, or may be acquired from two directions. Here, when acquiring from only one direction, it is acquired from the side of the patient's head including the dental arch that is the subject. The reason is the same as in the case of the scout view based on the linear scan transmission image described above.

  In any tomographic image capturing, the object is preferably acquired from two directions. This is because the three-dimensional position of the region of interest can be grasped by acquiring from two directions.

Next, another embodiment of the present invention will be described.
FIG. 17 is a schematic block diagram illustrating the overall configuration of an X-ray imaging apparatus M2 that is another embodiment.

  The apparatus M2 moves the optical system composed of the X-ray generator 11 and the X-ray detection unit 12 supported opposite to each other by the support unit 13a relative to the subject o held by the holding unit 13c. And a display unit 15a composed of a workstation, a personal computer, etc., an operation unit 15b, and an X-ray imaging control means 14 for controlling the apparatus M2.

  The moving means 13 can detect the X-ray generator 11 and the X-ray detector if the support frame 13a and the holding means 13c can be mechanically connected to the main body frame 16 fixed to the floor to establish a mutual positional relationship. In order to rotate the optical system with the unit 12 relative to the subject o, either the support unit 13a or the holding unit 13c may be rotated, and the axis of rotation of the optical system is relative to the floor surface. It may be a vertical configuration or a horizontal configuration.

  In this application, for convenience of explanation, terms such as horizontal and vertical are used assuming that the pivot axis A is set in the vertical direction with respect to the floor as in the above example. As described above, the direction of the turning axis A can be freely set, and is not limited to the meaning of horizontal and vertical with respect to the floor surface.

  The support portion 13a is configured as a turning arm connected to the rotation axis A, and an angle sensor S for detecting a rotation angle is attached. Further, the rotating shaft connecting portion of the swivel arm may be a swivel arm moving table that moves the entire swivel arm in the longitudinal direction of the swivel arm on a plane orthogonal to the rotation axis A, and X-ray generation is then performed. Since the ratio between the dimension from the container 11 to the subject o and the dimension from the subject o to the X-ray detection unit 12 can be changed, the projection magnification can be controlled.

  An axis moving table 13b attached to the main body frame 16 includes a rotation axis driving means 13h (not shown) for rotating the rotation axis A by a turning control motor (not shown), an X axis control motor (not shown), and a Y axis control motor (not shown). An XY table 13e that controls the position of the rotation axis A on a plane intersecting the rotation axis A by two-dimensional control (not shown), and an elevating means 13f that moves the XY table 13e up and down along the rotation axis; It has. The rotary shaft driving means 13h may be on the shaft moving base 13b, but may be on the instruction unit 13a side.

  The holding means 13 c includes a headrest that holds the head of the patient who is the subject o, a seating surface on which the patient sits, and the like, and is connected to another lifting means (not shown) provided on the main body frame 16. The elevating means includes an elevating control motor (not shown), and controls the position of the holding means 13c along the rotation axis A.

  With such a configuration of the moving means 13, the relative position between the rotation axis A connected to the support portion 13a and the holding means 13c is in two directions defined on a plane that intersects the axis of rotation of the optical system. Control is performed by three-dimensional control by two-dimensional control and one-dimensional control in the direction along the axis of rotation of the optical system. Effectively, this is controlled by position control by an XYZ table. May be. However, the position of the support portion 13a and the holding means 13c may be controlled by two XYZ tables. It should be noted that a stepping motor or the like that can control the rotation angle and the rotation speed is preferably used for each control motor of the moving means 13.

  The X-ray generator 11 and the X-ray detection unit 12 have the same configuration as that described in the first embodiment. That is, the X-ray generator 11 changes the shape of the X-ray cone beam irradiated by the X-ray tube 11a into a narrow groove-like space 11c corresponding to the X-slit beam B and a rectangular space corresponding to the X-ray wide-area beam BB. The X-ray slit beam B and the X-ray wide-area beam BB can be selectively switched and generated by controlling the irradiation field control means 11D for moving the primary slit plate 11b formed with 11d.

  The X-ray detector 12 comprises an X-ray detector 12c, a cassette moving means 12d, and an exposure field control means 12e provided with a secondary slit plate. The X-ray detector 12c includes an elongated first image sensor 12a and a rectangular second image sensor used for X-ray CT imaging along an axis that rotates the X-ray generator 11 and the X-ray detection unit 12. 12b is a removable cassette 12cc having a housing similar to that of a conventional X-ray film cassette. Therefore, the X-ray imaging apparatus M2 replaces the X-ray detector 12c with an X-ray film cassette. Can also be installed.

  The display unit 15a includes a workstation connected to the X-ray imaging control unit 14 via a communication cable, and stores a video memory 15c that stores image data transmitted from the X-ray imaging control unit 14, and a video memory 15c. A signal processing unit 15d that performs image processing on the stored image data, an image reconstruction unit 15e that reconstructs various images, a CRT 15f that displays images and various information, and the like are provided. The operation unit 15b includes a keyboard, a mouse, and the like of the workstation.

  The X-ray imaging control means 14 includes an X-ray tube control unit 14e that controls the tube voltage and current of the X-ray tube 11a constituting the X-ray generator 11, and a primary slit selection unit 14f that controls the irradiation field control means 11D. An imaging trajectory control means 14c for driving each control motor of the moving means 13, a positioning control means 14g for controlling the positioning of the support portion 13a by controlling the XY table 13e and the elevating means 13f, and X-ray detection A clock generation unit 14j that generates a clock for controlling the unit 12 and the imaging trajectory control means 14c, an operation panel 14k that simply displays information and receives an operation input, and stores a captured X-ray image for each frame. It consists of a frame memory 14n and a CPU 14p that integrates the entire X-ray imaging control means 14.

  Next, the basic operation of the device M2 will be described. The apparatus M2 provides an X-ray imaging apparatus that designates a specific region of interest s for the subject o and acquires an X-ray CT image of the region of interest s. For that purpose, the X-ray imaging control means 14 is provided. In summary, the scout view image acquired by photographing the subject o over a wide range with the first image sensor 12a is displayed on the display unit 15a, and the scout view image displayed on the display unit 15a is displayed by the operation of the operation unit 15b. In order to acquire the X-ray CT image of the designated region of interest s, the position of the support unit 13a and / or the holding means 13c is controlled in order to acquire the X-ray CT image of the specified region of interest s. I do.

  FIG. 18 is a flowchart showing a control procedure by the X-ray imaging control means 14 for performing the basic operation. According to this flowchart, the X-ray imaging control means 14 first executes an arrangement step for arranging the subject o at the reference position (step 401). That is, when a predetermined operation is received by the operation unit 15b or the operation panel 14k, the subject o is positioned at the reference position by moving the holding means 13c holding the subject o up and down.

  Then, by operating the operation unit 15b or the operation panel 14k, the panorama mode is selected as the imaging type of the scout view image, and when the imaging command is received, the panoramic tomographic image imaging is selected as the X-ray beam trajectory. The support portion 13a is positioned on a plane intersecting the axis of rotation of the optical system, the elongated gap 11c of the irradiation field control means 11D is selected, and the entire object o is photographed using the first image sensor 12a. A scout view image photographing step (steps 402 to 406) is executed.

  In the above, panoramic tomographic image capturing is performed to acquire a scout view image, but instead of the panoramic tomographic plane image, the position of the region of interest s is set using each of linear scan transmission images from two directions. By designating on the image from the direction, for example, coordinates may be explicitly designated for two orthogonal coordinate axes.

  When shooting of the scout view image is completed in this manner, the acquired image data is processed and reconstructed, the scout view image is displayed on the display unit 15a, and the cursor is interlocked with the mouse operation of the operation unit 15b. A region-of-interest specifying step (steps 407 to 409) for specifying the region s and selecting the shooting type for the main shooting is executed. The panoramic tomographic plane image displayed as the scout view image displayed here is the same as that described in the first embodiment.

  The region of interest s may be specified by a cursor that moves on the CRT 15f of the display unit 15a in accordance with the operation of the operation unit 15b. As the cursor, any of an arrow-shaped cursor, a cross-shaped cursor, a rectangular cursor that displays a region of interest frame may be used, or a cursor that combines them may be used. Thereby, the position of the region of interest s can be explicitly designated with respect to two coordinate axes orthogonal to each other on the panoramic tomographic plane image. Further, with respect to one coordinate axis in the thickness direction of the panoramic tomographic plane image, the coordinates near the center of the dentition thickness may be automatically designated based on the size of the dentition image.

  Thereafter, when an imaging command for main imaging is received from the operation unit 15b or the operation panel 14k, the position of the designated region of interest s is calculated, the imaging type of main imaging is determined, and normal X-ray CT imaging is performed. If there is, the normal X-ray CT imaging is selected as the trajectory of the X-ray beam, and the support portion 13a and / or the holding means 13c are moved on the plane intersecting the rotation axis of the optical system to turn the optical system. The axis is positioned so as to pass through the center point of the region of interest, and the X-ray detector 12c is slid forward or backward in the turning direction, so that the X-ray generator 11, the region of interest s, and the second image sensor 12b If the imaging type is offset scan CT imaging to be described later, the offset scan CT imaging is selected as the locus of the X-ray beam, and the support unit 13a and / or The holding means 13c is moved on a plane intersecting the axis of rotation of the optical system so that the axis of rotation of the optical system passes through the center point of the region of interest s, and the X-ray detector 12c is further rotated in the direction of rotation. The second image sensor 12b is slid forward or backward by a distance different from that in normal X-ray CT imaging so that the second image sensor 12b is offset from a straight line passing through the X-ray generator 11 and the region of interest s. Next, the height of the region of interest s is determined, and if the position of the region of interest s is higher than the reference position, the rectangular gap 11d of the irradiation field control means 11D is selected, and the support portion 13a is raised and / or held. By lowering the means 13c, the second image sensor 12b is positioned in the direction parallel to the axis of rotation of the optical system, and if the position of the region of interest s is lower than the reference position, the irradiation field control means 11 The rectangular gap 11d is selected and the support portion 13a is lowered and / or the holding means 13c is raised, thereby positioning the second image sensor 12b in a direction parallel to the axis of rotation of the optical system ( Steps 410-423) are executed. That is, in the imaging position adjustment step, the center coordinates of the region of interest specified on the panoramic tomographic plane image are referred to the positioning data obtained when the subject is positioned at the reference position in the placement step, and the spatial coordinates for position adjustment are obtained. Conversion is performed so that the axis of rotation of the optical system coincides with the center of the region of interest.

  Then, based on the positioning in the photographing position adjustment step, the support portion 13a is rotated, and the second image sensor 12b generates a transmission image including the entire region of interest s or a portion of a ratio of 1/2 or more at a predetermined angle. The main imaging steps (steps 423 and 424) for reconstructing an X-ray CT image with respect to the desired tomographic plane of the region of interest s are performed by performing image processing on the acquired transmission image.

  In the selection of the above-described imaging type, at least a panorama mode and a CT mode can be selected, and a normal CT mode and an offset scan CT mode can be selected as the CT mode. However, the linear scan mode or the like may be selected, and the region of interest s is designated on the CRT 15f of the display unit 15a on which the panoramic tomographic plane image is displayed while the panoramic mode is selected. Sometimes, the CT mode may be automatically selected.

  FIG. 19 is a plan view showing a locus of an X-ray beam for X-ray CT imaging, and shows a locus for offset scan CT imaging. At the time of offset scan CT imaging, the X-ray generator 11 and the X-ray detection unit 12 use the rotation axis A aligned with the center of the region of interest s as the axis of rotation, and the X-ray generator 11 and the region of interest. In a state in which the second image sensor 12b is offset with respect to a straight line passing through s, the second image sensor 12b rotates synchronously for at least one rotation or more, and a portion of a ratio of ½ or more of the region of interest s is the second image sensor 12b is always projected. It should be noted that the trajectory for offset scan CT imaging can be variously modified in addition to this.

  The scout view image of the present invention is intended to set a region of interest R that is a target for tomographic image capturing on the subject o, and for that purpose, it is sufficient that a specific part can be selected from the entire image. High-resolution images are not necessarily required. Therefore, it is desirable to configure the scout view image so that an appropriate resolution can be selected as necessary. Such a configuration is also valuable from the viewpoint of reducing the amount of exposure.

  In order to be able to select the resolution of the scout view image, a binning technique known as a conventional technique can be introduced. Basically, in this binning technique, if a CCD sensor is used as the first image pickup means S1, the control signal of the CCD constituting the charge transport portion of the sensor can be picked up at normal resolution and the other can be selected. This can be easily realized by differentiating from low-resolution shooting. More specifically, for example, in the process of bucket-relay charge transfer by the charge transfer unit after shooting at normal resolution, for example, four pixels arranged in a lattice form are changed to two pixels arranged vertically or horizontally. Alternatively, the photographic charges of the four pixels may be periodically overlapped so as to be one pixel.

  Note that the binning technique need not be limited to only the scout view, and may be used as appropriate in photographing a region of interest using a scout view image.

  FIG. 6 is a diagram showing an example of execution of such binning processing. 2 × 1 binning processing is performed on an original image (upper left panoramic tomographic plane image) photographed as a scout view image and photographing charges of the same resolution. Are shown (upper right), an image that has been subjected to 1 × 2 binning processing (lower left), and an image that has been subjected to 2 × 2 binning processing (lower right). Note that a vertically long image by 2 × 1 binning processing and a horizontally long image by 1 × 2 binning processing can be displayed on the display unit 14 with a correct aspect ratio by simple image processing such as thinning processing. Such image processing is normally performed because the resolution is originally different between the captured image and the image displayed on the display unit 14, and is not newly required for binning.

  The reduction in the exposure amount as an effect here is that the imaging charge after binning processing increases due to superposition if the imaging conditions are the same, but the X-ray generation unit 12 irradiates with an expectation of the increase. This is achieved as an effect of decreasing the dose or increasing the turning speed of the moving means 11. In either case, a similar decrease in the amount of X-ray exposure can be expected, but the stress of the subject who is the subject o becomes lighter when the turning speed is increased and the imaging time is shortened.

  A similar binning process can be introduced even when a CMOS sensor is employed as the image sensor. This will be briefly described below with reference to a circuit diagram for explaining the basic configuration of the CMOS sensor.

  FIG. 6A is a simplified diagram of a circuit for four pixels of a CMOS sensor. This circuit is a MOS transistor that constitutes a capacitor corresponding to each of four pixels adjacent in a grid between lines LI and LO1, or between lines LI2 and LO2, and a switch for reading out the photographic charge accumulated in each capacitor. A switch SW1 composed of M1 to M4, sense amplifiers A1 to A3 for generating voltage signals corresponding to the read photographing charges, and MOS transistors for selectively connecting the lines LO1 and LO2 to the sense amplifiers A1 to A3. , SW2.

  When performing normal shooting with this circuit, first, the switches SW1 and SW2 are controlled so that the lines LO1 and LO2 are connected to the sense amplifiers A1 and A2, respectively. After the image is captured, first, the line K1 is activated to read out the charges Q1 and Q2 to the lines LO1 and LO2, respectively. The voltage signals generated by the sense amplifiers A1 and A2 at this time are converted to A / The digital signal is sampled and converted by a D converter or the like, and then the lines LO1 and LO2 are once discharged, and then the line K2 is activated. Then, since voltage signals corresponding to the charges Q3 and Q4 are generated in the sense amplifiers A1 and A2, they are sampled and converted into digital signals. By such an operation, the photographing charges Q1 to Q4 of all the pixels of the CMOS sensor are converted into digital signals, respectively.

  When performing the 2 × 1 binning process, the switches SW1 and SW2 are controlled so that the lines LO1 and LO2 are connected to the sense amplifiers A1 and A2, respectively. After the image is captured, the lines K1 and K2 are activated simultaneously, and both the photographic charges Q1 and Q3 are read and superimposed on the line LO1, and at the same time, both the photographic charges Q2 and Q4 are read and superimposed on the line LO2. . Then, the sense amplifier A1 generates a voltage signal according to the superimposed charge Q1 + Q3, and the sense amplifier A2 generates a voltage signal according to the superimposed charge Q2 + Q4. Sampling and A / D conversion may be performed.

  When performing the 1 × 2 binning process, the switches SW1 and SW2 are controlled so that the lines LO1 and LO2 are both connected to the sense amplifier A3. Then, after the image is captured, first, the line K1 is activated, and the imaging charges Q1 and Q2 are read and superimposed on the lines LO1 and LO2 that are short-circuited at this time. As a result, the sense amplifier A3 generates a voltage signal corresponding to the superimposed charge Q1 + Q2, and therefore samples and A / D converts the voltage signal. Thereafter, the lines LO1 and LO2 are once discharged, the line K2 is activated, and the photographing charges Q3 and Q4 are read and superimposed on the lines LO1 and LO2. As a result, the sense amplifier A3 generates a voltage signal corresponding to the superimposed charge Q3 + Q4, and the voltage signal is sampled and A / D converted.

  When performing the 2 × 2 binning process, the switches SW1 and SW2 are controlled so that both the lines LO1 and LO2 are connected to the sense amplifier A3. After the image is captured, the lines K1 and K2 are activated at the same time, and the imaging charges Q1, Q2, Q3, and Q4 are all read and superimposed on the lines LO1 and LO2 that are short-circuited to each other at this time. As a result, the sense amplifier A3 generates a voltage signal corresponding to the superimposed charges Q1 + Q2 + Q3 + q4. Therefore, the voltage signal may be sampled and A / D converted.

  The idea of the present invention can also be applied to an X-ray imaging apparatus used for purposes other than medical use. That is, even for industrial use, there is a case where non-destructive inspection imaging is performed after scouting, and it is desirable to apply the idea of the present invention to an X-ray imaging apparatus for such use.

1 is a block diagram illustrating a schematic configuration of an X-ray imaging apparatus according to an embodiment. The schematic diagram explaining the mechanism of the X-ray generator used for the X-ray imaging apparatus of FIG. FIG. 2 is an external view illustrating an example of a basic configuration of an X-ray detector used in the X-ray imaging apparatus of FIG. 1. The top view explaining the imaging | photography trajectory to which an X-ray generator and an X-ray detector move synchronously when image | photographing a linear scan transmission image. The example of the linear scan transmission image obtained by imaging | photography by the imaging | photography trajectory of FIG. The drawing explaining the principle of a binning process. The simplified circuit diagram of a CMOS sensor. The example of the panoramic tomographic plane image obtained by imaging | photography by the imaging | photography trajectory of FIG. (A), (b) The top view explaining two types of imaging | photography trajectories to which an X-ray generator and an X-ray detector move synchronously when imaging a linear tomographic plane image. FIG. 3 is a plan view for explaining an imaging trajectory in which an X-ray generator and an X-ray detector move synchronously when imaging an X-ray CT image. The flowchart explaining an example of a series of operation | movement which consists of imaging | photography of a scout view image, imaging | photography classification selection, and imaging | photography of a tomographic plane image. The flowchart explaining the other example of a series of operation | movement which consists of imaging | photography of a scout view image, imaging | photography classification selection, and imaging | photography of a tomographic plane image. The flowchart explaining the other example of a series of operation | movement which consists of imaging | photography of a scout view image, imaging | photography classification selection, and imaging | photography of a tomographic plane image. The perspective view of the X-ray imaging apparatus used as a more concrete Example. The top view of the X-ray imaging apparatus of FIG. 10 which added the cephalometric image imaging means. The side view of the X-ray imaging apparatus of FIG. 10 which added the cephalometric image imaging means. (A), (b) is sectional drawing which shows the structure of the X-ray generator used for the X-ray imaging apparatus of FIG. 10, respectively, and the drive part perspective view of a primary slit. The schematic block diagram explaining the whole structure of the X-ray imaging apparatus which is another Example. The flowchart which shows the control procedure for the X-ray imaging apparatus which is another Example to perform basic operation | movement. (A), (b) is a top view which respectively shows the locus | trajectory for normal X-ray CT imaging | photography, a locus | trajectory, and an offset scan CT imaging | photography. The flowchart explaining the other example of a series of operation | movement which consists of imaging | photography of a scout view image, imaging | photography classification selection, and imaging | photography of a tomographic plane image. The flowchart explaining the other example of a series of operation | movement which consists of imaging | photography of a scout view image, imaging | photography classification selection, and imaging | photography of a tomographic plane image. A table that summarizes the possible combinations of scout view images and tomographic imaging. The figure which shows the imaging | photography principle which acquires a scout view image using a 2nd image sensor with a X-ray slit beam. The figure which shows the envelope which the locus | trajectory of an X-ray slit beam draws at the time of panoramic tomographic plane image photography. (A)-(c) is an example of the shape of the detection surface of a 1st image sensor and a 2nd image sensor, respectively, (d) is a modification of an X-ray detector. (A), (b) is an example of a whole jaw panoramic tomographic plane image, respectively.

Explanation of symbols

11 X-ray generator 12a First X-ray image sensor 12b Second X-ray image sensor 14 X-ray imaging control means 15 Imaging type selection means 15a Display unit B X-ray slit beam BB X-ray wide-area beam M, M2 X X-ray equipment o Subject s Area of interest

Claims (12)

An X-ray generator capable of selectively switching between an X-ray slit beam and an X-ray wide-area beam;
A first X-ray image sensor that is vertically long and has a small width in order to receive an X-ray slit beam and capture a transmission image of a subject;
An X-ray imaging apparatus comprising a second X-ray image sensor that receives an X-ray wide-area beam and captures a transmission image of a subject,
A display unit for displaying a scout view image of a subject generated using the X-ray slit beam and the first X-ray image sensor;
An imaging type selection unit that selects a desired region of interest on the scout view image displayed on the display unit, and further selects an imaging type of a tomographic plane image prepared in advance for the region of interest;
While synchronously moving the X-ray generator and one of the first and second X-ray image sensors along an imaging trajectory corresponding to the imaging type selected by the imaging type selection unit, An X-ray imaging apparatus having a scout view function including an X-ray imaging control means for performing X-ray imaging. In claim 1,
An X-ray imaging apparatus having a scout view function that includes at least one of a linear tomographic plane image, a panoramic tomographic plane image, and an X-ray CT image as the tomographic plane imaging type. In claim 1,
A display unit for displaying a scout view image of a subject generated using the second X-ray image sensor;
An imaging type selection unit that selects a desired region of interest on the scout view image displayed on the display unit, and further selects an imaging type of a tomographic plane image prepared in advance for the region of interest;
While moving the X-ray generator and any one of the first image sensor and the second image sensor synchronously along an imaging trajectory corresponding to the imaging type selected by the imaging type selection unit, An X-ray imaging apparatus having a scout view function including an X-ray imaging control means for performing X-ray imaging. An X-ray generator capable of generating either an X-ray slit beam or an X-ray broad beam;
An X-ray imaging apparatus including an X-ray image sensor that receives an X-ray slit beam and images a subject and receives an X-ray wide-area beam and images the subject,
A display unit for displaying a scout view image of a subject generated using either the X-ray slit beam or the X-ray wide-area beam and the X-ray image sensor;
An imaging type selection unit that selects a desired region of interest on the scout view image displayed on the display unit, and further selects an imaging type of a tomographic plane image prepared in advance for the region of interest;
X-ray imaging for performing X-ray imaging while synchronously moving the X-ray generator and the X-ray image sensor along an imaging trajectory corresponding to the imaging type selected by the imaging type selection means An X-ray imaging apparatus having a scout view function including a control means. In any one of Claims 3 and 4,
An X-ray imaging apparatus having a scout view function in which the scout view image includes a scan transmission image of a subject. In any one of Claims 3-5,
An X-ray imaging apparatus having a scout view function including a panoramic tomographic plane image or two-way simple imaging in the scout view image. In any one of Claims 3-6,
An X-ray imaging apparatus having a scout view function that includes at least one of a linear tomographic plane image, a panoramic tomographic plane image, and an X-ray CT image as the tomographic plane image type. The X-ray generator and the X-ray detector supported opposite to each other by the support unit are provided with moving means for rotating relative to the subject held by the holding means, and the moving means is operated to operate the X-ray of the subject. In a medical X-ray imaging apparatus that captures a line image,
It has an irradiation field control means, and by controlling the shape of the X-ray cone beam irradiated by the X-ray tube by this irradiation field control means, the X-ray slit beam and the X-ray wide-area beam are selectively switched and generated. An X-ray generator enabled,
In order to capture the panoramic tomographic image of the subject by receiving the X-ray slit beam, the X-ray CT image of the subject is captured by receiving the first long X-ray image sensor having a small width and the wide X-ray beam. An X-ray detector comprising an X-ray detector provided with a second X-ray image sensor;
A display unit for displaying a panoramic tomographic plane image of a subject generated using the X-ray slit beam and the first X-ray image sensor as a scout view image;
In order to select a desired region of interest on the scout view image displayed on the display unit, and to acquire an X-ray CT image of the selected region of interest by the second X-ray image sensor, the support unit and / or Or an X-ray imaging apparatus comprising control means for controlling the position of the holding means. In claim 8,
The position control of the support portion and / or the holding means is two-dimensional two-dimensional control defined on a plane intersecting with an axis for turning the X-ray generator and the X-ray detection portion. X-ray imaging device. In claim 8,
Position control of the support part and / or the holding means is performed in two directions defined on a plane intersecting with an axis for turning the X-ray generator and the X-ray detection part, and in one direction parallel to the axis. An X-ray imaging apparatus characterized by three-dimensional control. In any one of Claims 8-10,
The second X-ray image sensor is offset forward or backward in the turning direction of the X-ray detector, and the selected region of interest is always projected at a predetermined ratio or more to perform X-ray CT imaging of the region of interest. An X-ray imaging apparatus characterized by that. In any one of Claims 1-11,
The X-ray image sensor is composed of any one of an X-ray image intensifier, a MOS sensor, a CMOS sensor, a TFT sensor, a CCD sensor, a MIS type sensor, and an X-ray solid-state imaging device. Shooting device.

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