JP5776520B2 - Radiography equipment - Google Patents

Description

  The present invention relates to a radiation imaging apparatus that performs imaging of a subject by irradiating radiation, and particularly relates to a radiation imaging apparatus that continuously acquires a plurality of images by continuously performing a plurality of radiation irradiations.

  A medical institution is equipped with a radiation imaging apparatus that images a subject by irradiating radiation. Such a radiographic apparatus is used for imaging a digestive organ of a subject. A contrast agent (barium) is used for such imaging.

  In imaging of a digestive system of a subject using a contrast agent, imaging of the esophagus is performed a plurality of times while the contrast agent is passing. The esophagus is photographed multiple times. The image taken at this time is displayed on the monitor each time. When photographing of the esophagus is completed, a plurality of photographed images are divided and displayed on a monitor as shown in FIG. According to the example of FIG. 14, the esophagus is photographed four times, and the image displayed on the monitor is obtained in each photographing. By displaying all of the captured images at once on the monitor, it is possible to easily compare images at different capturing points (see, for example, Patent Document 1). The surgeon takes a picture of the stomach after taking the esophagus.

  Each photography of the esophagus was performed under similar conditions. However, the images obtained by each imaging do not always reflect the esophagus of the subject in the same way. That is, the brightness and contrast may not be the same between images. Such a difference in reflection between images is caused by, for example, image adjustment automatically performed by the radiation imaging apparatus or a difference in how the contrast agent is reflected during imaging.

  Differences in brightness and contrast between images hinder the comparison of images. Therefore, according to the conventional radiation imaging apparatus, each of the images divided and displayed on the monitor can be manually adjusted. That is, the radiation imaging apparatus includes an input device for inputting an operator's instruction, and can individually adjust the brightness and contrast of each image on the monitor based on the operator's designation. Therefore, after completing the esophageal imaging, the surgeon should prepare the stomach for imaging after comparing each image divided and displayed on the monitor and adjusting the contrast and contrast of images that differ from the others. become.

  As described above, according to the conventional configuration, a plurality of images cannot be compared unless a series of photographing is completed. Only one recently captured image is displayed on the monitor before the completion of imaging, and no previous image is displayed.

JP 2000-232976 A

However, the conventional radiographic apparatus has the following problems.
That is, the conventional radiation imaging apparatus cannot compare images acquired in a series of imaging until the series of imaging is completed, which hinders a rapid imaging operation.

  If a plurality of images are adjusted after the esophagus has been imaged four times, the image adjustment takes a long time. Then, after completing the esophageal imaging, it is not possible to immediately start the next imaging, taking time to adjust the image, even if an attempt is made to take an image of the stomach. In other words, the contrast medium reaches the stomach while taking time to adjust the image, and the operator misses the opportunity for imaging, and in some cases, the examination may be restarted. As described above, the conventional radiation imaging apparatus has a problem that the imaging time is prolonged.

  In addition, since the comparison of images acquired in a series of shootings can be performed only after the shooting is completed, the shooting time is prolonged even in other shooting modes. That is, some conventional radiographic apparatuses perform long imaging in which a plurality of strip images are connected to obtain a single long image. Such a radiation imaging apparatus captures a plurality of strip images while shifting the capturing position, and after the capturing is completed, a single long image in which the strip images are joined together is generated.

  It is assumed that a series of strip images has been started in the radiation imaging apparatus. On the monitor at this time, only one recently taken strip image is displayed, and the previous strip images are not displayed. Therefore, the surgeon cannot accurately know whether or not the strip image has been correctly shot during shooting.

  During imaging of a series of strip images, the surgeon can visually recognize a single strip image through a monitor. However, even if there is no problem as a single strip image, a long image with excellent visibility may not be obtained when the strip images are joined together. Problems that can be recognized for the first time after joining such strip images include image shift due to body movement of the subject. The displacement of the subject image that occurs between the strip images is difficult to detect even if the surgeon looks at the strip images one by one. In other words, according to the conventional configuration, the operator first notices the poor visibility of the long image by connecting all the strip images and acquiring the long image. Then, it is necessary to redo the shooting of the strip image from the beginning, and the shooting time becomes longer.

  The present invention has been made in view of such circumstances, and an object of the present invention is to take trouble in radiography in a radiography apparatus that continuously obtains a plurality of images by continuously performing a plurality of radiation irradiations. Is to provide a radiation imaging apparatus with reduced operability and excellent operability.

The present invention has the following configuration in order to solve the above-described problems.
That is, the radiographic apparatus according to the present invention includes a radiation source that irradiates radiation, a detection unit that detects radiation, and a detection time point based on detection signals that the detection unit sequentially outputs when the radiation source continuously emits radiation. An image generation means for generating a plurality of different images, an array display means for displaying the image generated this time and a previously generated image side by side each time an image is generated, and (A) the array display means An input unit for inputting an operator's instruction regarding adjustment of the displayed image, and (B) an image adjustment process is performed on one of the images displayed on the array display unit based on the input of the input unit. and an image adjusting means for sending the image after the sequence display section, the image adjustment means, according to an instruction of the operator entered after each shot image, that perform adjustment processing of the image in between shooting That features It is intended to.

  [Operation / Effect] The above-described configuration includes array display means for displaying a plurality of images at different shooting points in time. The display of the array display means is performed every time an image is generated, and the image generated this time and the previously generated image are displayed side by side. By adopting such a configuration, it is possible to provide a radiation imaging apparatus with reduced operability and excellent operability.

  That is, the surgeon can individually perform image adjustment processing between image captures by comparing the images displayed side by side on the array display means. According to the conventional configuration, the image adjustment processing is performed when a series of photographing is completed. Therefore, according to the conventional configuration, the surgeon must perform adjustment processing on a plurality of images at once after a series of imaging is completed, and the next operation cannot be quickly started. However, according to the configuration of the present invention, the image adjustment processing is almost finished when a series of photographing is completed. This is because the adjustment process is possible between shootings. That is, since the operator can start the next operation only by adjusting the last image taken, the radiation imaging apparatus of the present invention has reduced operability and is excellent in operability.

  In the above-described radiation imaging apparatus, it is more preferable that a display unit that displays a single image and updates the image every time the image is captured is provided separately from the array display unit.

  [Operation / Effect] The above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. By providing a display means for displaying a single image and updating the image every time the image is captured, a radiation imaging apparatus capable of capturing images while confirming the details of each image can be provided.

Further, the radiographic apparatus according to the present invention includes a radiation source that irradiates radiation, a detection unit that detects radiation, and a detection time point based on detection signals that are sequentially output by the detection unit when the radiation source continuously emits radiation. An image generating means for generating a plurality of different images, an array displaying means for displaying the image generated this time and the previously generated image side by side each time an image is generated, and (C) a radiation source. Radiation source moving means for moving the specimen, (D) radiation source movement control means for controlling the radiation source moving means, and (E) movement of the radiation source imaged while the radiation source is moved relative to the subject. A composite image is generated by joining each of the elongated images in the direction perpendicular to the direction of movement, and a plurality of images generated by the image generation means are arranged by displaying the composite image on the arrangement display means And an image synthesizing means for displaying side by side in shown means, image combining means, characterized that you generate a synthesized image by connecting side by side in order of the generated to the current generated image from first generated image It is what.

  [Operation / Effect] The above-described configuration includes array display means for displaying a plurality of images at different shooting points in time. The display of the array display means is performed every time an image is generated, and the image generated this time and the previously generated image are displayed side by side. By adopting such a configuration, it is possible to provide a radiation imaging apparatus with reduced operability and excellent operability.

That is, the surgeon can know whether shooting is smooth between image shootings by comparing images displayed side by side when shooting a long image in which a plurality of images are taken and connected together. it can. According to the conventional configuration, the stitching process of images is performed when a series of photographing is completed. In the conventional configuration, the surgeon can only confirm the image captured just before the image capturing. Therefore, even if the subject moves during the imaging, the surgeon is not aware of this movement, and notices the image inconsistency only after viewing the long image displayed on the array display means after the imaging is completed. Then, you will have to start shooting again. According to the present invention, a composite image in which images are stitched between a series of image capturing operations is displayed on the array display means. Therefore, the operator can quickly notice the movement of the subject and can immediately stop the imaging. As described above, the radiation imaging apparatus of the present invention is excellent in operability by reducing the labor of imaging.
In addition, if the image synthesis means generates a composite image by arranging and joining the first generated image to the current generated image in the order of generation, the surgeon can shoot while recognizing the entire image of the operator. You can check the progress.

  The radiation imaging apparatus includes a detector moving unit that moves the detecting unit relative to the subject, and a detector movement control unit that controls the detector moving unit. The radiation source and the detecting unit are mutually connected. It is more desirable to move relative to the subject while maintaining the relative position.

  [Operation / Effect] The above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. If the radiation source and the detection means are imaged while moving relative to the subject while maintaining the relative positions of each other, a wider range of long-time imaging is possible.

  In the above-described radiographic apparatus, the image synthesizing unit excludes the first elongated image generated when the generated image exceeds a predetermined number indicating the number of images that can be displayed on the array display unit. It is more desirable to generate a composite image by selecting a predetermined number of images from the most recently generated image each time an image is generated and connecting them together.

  [Operation / Effect] The above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. When the number of images generated by the image composition means exceeds a predetermined number indicating the number of images that can be displayed on the array display means, a predetermined number of images are selected from the most recently generated images, and these are connected to generate a composite image. By doing so, it is possible to avoid a situation in which recently captured images are not displayed on the array display means and are not displayed.

  In the above-described radiation imaging apparatus, it is more preferable that the radiation imaging apparatus includes a radiation source control unit that gives an instruction of an irradiation condition to the radiation source.

  [Operation / Effect] The above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. The present invention is particularly suitable when a plurality of photographings are performed under the same irradiation conditions. That is, the radiographic apparatus is configured so that the images can be compared between the images as in the present invention in an imaging mode in which the appearance of the subject on the image differs despite the same imaging. In this way, the radiation imaging apparatus has reduced operability for imaging and has excellent operability.

  The above-described configuration is provided with array display means for displaying a plurality of images at different shooting points in time. The display of the array display means is performed every time an image is generated, and the image generated this time and the previously generated image are displayed side by side. By adopting such a configuration, it is possible to provide a radiation imaging apparatus with reduced operability and excellent operability. That is, if the radiation imaging apparatus is configured in this way, the surgeon can quickly move to the next operation. In addition, it is possible to quickly notice shooting problems and redo shooting at an early stage.

1 is a functional block diagram illustrating a configuration of an X-ray imaging apparatus according to Embodiment 1. FIG. FIG. 6 is a schematic diagram illustrating display on a display unit according to the first embodiment. FIG. 6 is a schematic diagram illustrating display on a display unit according to the first embodiment. FIG. 6 is a schematic diagram illustrating display on a display unit according to the first embodiment. 3 is a flowchart for explaining the operation of the X-ray imaging apparatus according to Embodiment 1; 6 is a functional block diagram illustrating a configuration of an X-ray imaging apparatus according to Embodiment 2. FIG. FIG. 6 is a perspective view illustrating a collimator according to a second embodiment. FIG. 10 is a schematic diagram for explaining advantages of long shooting according to the second embodiment. FIG. 10 is a schematic diagram for explaining strip image capturing according to the second embodiment. FIG. 9 is a schematic diagram illustrating display on a display unit according to Example 2. 6 is a flowchart illustrating an operation of the X-ray imaging apparatus according to the second embodiment. It is a schematic diagram explaining the display of the display part which concerns on 1 modification of this invention. It is a schematic diagram explaining the display of the display part which concerns on 1 modification of this invention. It is a schematic diagram explaining the display of the image which concerns on the conventional structure.

  Hereinafter, examples of the present invention will be described. X-rays in the examples correspond to the radiation of the present invention. FPD is an abbreviation for flat panel detector.

<Overall configuration of X-ray imaging apparatus>
First, the configuration of the X-ray imaging apparatus 1 according to the first embodiment will be described. As shown in FIG. 1, the X-ray imaging apparatus 1 includes a top plate 2 on which a subject M in a supine position is placed, an X-ray tube 3 that irradiates X-rays provided on the top plate 2, and a top plate. 2 and an FPD 4 for detecting X-rays provided on the lower side. The FPD 4 is a rectangle having four sides along either the body axis direction A or the body side direction S of the subject M. The X-ray tube 3 irradiates the FPD 4 with a quadrangular pyramid-shaped X-ray beam that spreads radially. The FPD 4 receives the X-ray beam on the entire surface. On the detection surface 4a for detecting X-rays of the FPD 4, X-ray detection elements are two-dimensionally arranged in the body axis direction A and the body side direction S. The support column 5 supports the X-ray tube 3 and the FPD 4. The X-ray tube 3 corresponds to the radiation source of the present invention, and the FPD 4 corresponds to the detection means of the present invention.

  The X-ray tube control unit 6 is provided for the purpose of controlling the X-ray tube 3 with a predetermined tube current, tube voltage, and pulse width. The FPD 4 detects X-rays emitted from the X-ray tube 3 and transmitted through the subject M, and generates a detection signal. This detection signal is sent to the image generation unit 11, where an image P0 in which a projection image of the subject M is reflected is generated. The generated image P0 is sent to the display unit 25a and the array display unit 25, and the display unit 25a and the array display unit 25 display the image P0 by different display methods. The X-ray tube control unit 6 corresponds to the radiation source control unit of the present invention, and the image generation unit 11 corresponds to the image generation unit of the present invention. The display unit 25a corresponds to the display unit of the present invention, and the array display unit 25 corresponds to the array display unit of the present invention.

  The image adjustment unit 12 performs an image adjustment process on the image P 0 generated by the image generation unit 11 and sends the processed image to the array display unit 25. The image adjustment unit 12 performs an adjustment process on one of a plurality of images P0 displayed on the array display unit 25 at different shooting time points. The adjustment process performed by the image adjustment unit 12 is, for example, contrast adjustment and brightness adjustment. The image adjustment unit 12 corresponds to the image adjustment unit of the present invention.

  A method of displaying an image on the display unit 25a and the array display unit 25 will be described. FIG. 2 shows a display state after the first image P0a is taken. When the image P0a is captured and the image generation unit 11 generates the image P0a, the display unit 25a displays the image P0a generated this time. This display continues for a while.

  The display on the array display unit 25 in FIG. 2 will be described. On the array display unit 25, the image P0a generated this time is displayed small on a part of the array display unit 25. The array display unit 25 is provided with a margin for displaying an image P0b to be shot.

  FIG. 3 shows a display state after the second image P0b is taken. When the image P0b is shot and the image generation unit 11 generates the image P0b, the display unit 25a displays the image P0b generated this time instead of the image P0a. This display continues for a while.

  The display on the array display unit 25 in FIG. 3 will be described. On the array display unit 25, the image P0b generated this time is displayed small on a part of the array display unit 25. The array display unit 25 is provided with a margin for displaying an image P0 to be shot. As can be seen from FIG. 3, the image P0b generated this time and the image P0a generated previously are displayed side by side on the array display unit 25. At this point, the surgeon can complete imaging of the image P0 or can continue imaging of the image P0. 2 and 3, only two images P0 are generated. However, the array display unit 25 displays an image generated this time and a previously generated image side by side every time the image P0 is generated. To continue.

  An image adjustment method in Embodiment 1 will be described. The left side of FIG. 4 shows a state where three images P0 at different shooting points are displayed on the array display unit 25. The image P0 displayed by shading in the array display unit 25 on the left side of FIG. 4 is a darker image of the subject than the other images P0. As described above, when the appearance of the subject is different among the plurality of images P0 displayed on the array display unit 25, it is difficult for the operator to compare the images P0. Therefore, the surgeon gives the image adjustment unit 12 an instruction (adjustment of image processing) regarding the adjustment of the image displayed on the array display unit 25 to the image adjustment unit 12 through the mouse attached to the console 26 of the X-ray imaging apparatus. be able to. The console 26 corresponds to input means of the present invention.

  When the surgeon wants to adjust the brightness of one of the images P0 on the left side of FIG. 4, the surgeon moves the mouse pointer K displayed on the array display unit 25 to a position overlapping the target image P0, Press the left mouse button. Then, as shown by the thick frame on the left side of FIG. 4, the image adjustment unit 12 selects one of the images P0 displayed on the array display unit 25.

  The right side of FIG. 4 shows the selected image P0 in an enlarged manner. When the surgeon moves the pointer K upward in the image selection state (see the solid arrow on the right side of FIG. 4), the image adjustment unit 12 performs image processing so as to increase the brightness of the selected image P0. .

  Incidentally, when the surgeon moves the pointer K downward in the image selection state, the image adjustment unit 12 performs image processing so that the luminance of the selected image P0 is darkened. Similarly, when the surgeon moves the pointer K to the right in the image selection state, the image adjustment unit 12 performs image processing so as to enhance the contrast of the selected image P0, and the surgeon moves the pointer K. When moved to the left, the image adjustment unit 12 performs image processing so that the contrast of the selected image P0 is lost (see the dashed arrow on the right side of FIG. 4). In this way, the image adjustment unit 12 performs an image adjustment process on one of the images P0 displayed on the array display unit 25. Note that when the surgeon releases the press of the left mouse button, the image adjustment unit 12 cancels the selection of the image P0.

  The console 26 is provided for the purpose of inputting an instruction such as an X-ray irradiation start by the operator. The main control unit 27 is provided for the purpose of comprehensively controlling each control unit. The main control unit 27 is configured by a CPU, and realizes the control units 6 and the units 11, 11a, and 12 by executing various programs. Further, each of the above-described units may be divided and executed by an arithmetic device that takes charge of them. The storage unit 28 stores all parameters relating to control of the X-ray imaging apparatus 1 such as parameters used for image processing.

<Operation of X-ray imaging apparatus>
Next, the operation of the X-ray imaging apparatus will be described with reference to FIG. In this operation description, four images P0 are taken. This number of images can be designated by the surgeon to the X-ray imaging apparatus through the console 26 before imaging. The array display unit 25 changes the size and arrangement of the image P0 displayed on the array display unit 25 in accordance with the designated number of shots. The subsequent operation is aimed at photographing the esophagus of the subject.

  As an X-ray imaging operation, first, the subject M is placed on the top 2 (placement step S1), and four images P0 are captured (first image capturing step S2, second image capturing step S3). , Third image photographing step S4, fourth image photographing step S5). Hereinafter, these steps will be described in order.

<Installation step S1, first image photographing step S2>
First, a subject M to which a contrast medium (barium) is orally administered is placed on the top 2. When the surgeon gives an instruction to start imaging through the console 26, the console 26 sends the instruction to the X-ray tube controller 6. The X-ray tube control unit 6 reads out imaging conditions for imaging that are stored in the storage unit 28. Then, the X-ray tube control unit 6 causes the X-ray tube 3 to irradiate X-rays under imaging conditions for imaging. This X-ray irradiation is a single pulse irradiation. The display unit 25a and the array display unit 25 display the image P0a generated by the image generation unit 11 this time (see FIG. 2).

<Second Image Shooting Step S3>
When the surgeon instructs to take the second image P0b through the console 26, the console 26 sends the instruction to the X-ray tube controller 6. Then, the X-ray tube control unit 6 causes the X-ray tube 3 to irradiate X-rays under imaging conditions for imaging. This X-ray irradiation is a single pulse irradiation performed under the same irradiation conditions as the first imaging. The display unit 25a and the array display unit 25 display the image P0b generated this time by the image generation unit 11 side by side on the image P0a generated last time (see FIG. 3).

<Third Image Shooting Step S4, Fourth Image Shooting Step S5>
Thereafter, similarly, a third image and a fourth image are generated. At this time, the array display unit 25 displays the newly captured image P0 side by side with the previously captured image P0. The display unit 25a exclusively displays a single image P0, and each time the image P0 is captured. The display of the image P0 is continuously updated to a new one.

  After the second image capturing step S3, the third image capturing step S4, and the fourth image capturing step S5, the surgeon compares the image P0 captured this time with the image P0 captured last time through the array display unit 25. (See FIG. 4). The surgeon can perform image adjustment processing through the console 26 after each photographing.

  In conventional shooting, image adjustment processing can be performed only after four images have been shot. Therefore, the surgeon must adjust the plurality of images P0 collectively after taking the image P0. In the present invention, when a plurality of images P0 having different shooting times are acquired, the images P0 are compared between the shooting times of the images P0. Therefore, the image adjustment processing is performed in a distributed manner between the images P0. become.

  As described above, the above-described configuration includes the array display unit 25 that displays a plurality of images at different shooting points in time. The display of the array display unit 25 is performed every time the image P0 is generated, and the image P0 generated this time and the previously generated image P0 are displayed side by side. By adopting such a configuration, it is possible to provide an X-ray imaging apparatus with reduced operability and excellent operability.

  That is, the surgeon can individually perform the adjustment process of the image P0 through the console 26 between image capturing by comparing the images P0 displayed side by side on the array display unit 25. According to the conventional configuration, the image adjustment processing is performed when a series of photographing is completed. Therefore, according to the conventional configuration, the surgeon must perform adjustment processing on a plurality of images at once after a series of imaging is completed, and the next operation cannot be quickly started. However, according to the configuration of the present invention, the image adjustment processing is almost finished when a series of photographing is completed. This is because the adjustment process is possible between shootings. That is, since the operator can start the next operation only by adjusting the last image P0, the X-ray imaging apparatus of the present invention reduces the time and effort of imaging and has excellent operability. .

  If a display unit 25a is provided that displays a single image and updates the image every time the image is captured, the image can be captured while confirming the details of each image.

  Subsequently, an X-ray imaging apparatus according to Embodiment 2 will be described. Example 2 is a configuration in which the X-ray tube 3 and the FPD 4 move relative to the subject while maintaining their relative positions, and in a direction orthogonal to the moving direction of the X-ray tube 3 and the FPD 4 relative to the subject. In this configuration, the long strip image P1 is connected in the moving direction to generate a long image.

<Overall configuration of X-ray imaging apparatus 10>
The overall configuration of the X-ray imaging apparatus 10 according to the second embodiment is shown in FIG. Among the units shown in FIG. 6, the top plate 2, the X-ray tube 3, the FPD 4, the X-ray tube control unit 6, the image generation unit 11, the console 26, the main control unit 27, and the storage unit 28 are described in the first embodiment. Already explained. In the second embodiment, the image adjustment unit 12 and the display unit 25a in FIG. 1 are not necessarily required.

  The X-ray tube 3 is provided with a collimator 3a that limits the X-ray irradiation direction. The collimator 3a can adjust the opening degree. As shown in FIG. 7, the collimator 3a has a pair of leaves 3b that move mirror-symmetrically with respect to the central axis C, and another pair of leaves 3b that also move mirror-symmetrically with respect to the central axis C. I have. The collimator 3a can move the leaf 3b to irradiate the entire detection surface of the FPD 4 with the cone-shaped X-ray beam B. For example, only the central portion of the FPD 4 has a fan-shaped X-ray beam B. Can also be irradiated. The central axis C is also an axis indicating the center of the X-ray beam B. One of the pairs of leaves 3b is for adjusting the spread in the body axis direction A of the X-ray beam having a quadrangular pyramid shape, and the other pair of leaves 3b is the body side direction S of the X-ray beam. It is to adjust the spread of. When the X-ray tube 3 is moved, the collimator 3 a is also moved along with the X-ray tube 3.

  The X-ray tube moving mechanism 7 is provided for the purpose of moving the X-ray tube 3 in the body axis direction A of the subject (see FIG. 1). The X-ray tube movement control unit 8 controls the X-ray tube movement mechanism 7. The FPD moving mechanism 9 is provided for the purpose of moving the FPD 4 in the body axis direction A of the subject. The FPD movement control unit 10 controls the FPD movement mechanism 9. The X-ray tube 3 and the FPD 4 can move back and forth in the body axis direction A with respect to the subject while maintaining their relative positions by the X-ray tube moving mechanism 7 and the FPD moving mechanism 9. The X-ray tube moving mechanism 7 corresponds to the radiation source moving means of the present invention. The X-ray tube movement control unit 8 corresponds to the radiation source movement control means of the present invention, and the FPD movement mechanism 9 corresponds to the detector movement means of the present invention. The FPD movement control unit 10 corresponds to detector movement control means of the present invention.

  The image synthesizing unit 13 generates a composite image P2 and a long image P3 by arranging and joining the elongated strip images P1 in the body side direction S generated by the image generating unit 11 in the body axis direction A in the order of photographing. . The composite image P2 is a confirmation image that is sequentially generated while a plurality of strip images P1 are being photographed. The long image P3 is generated after all the strip images P1 have been photographed. This is a diagnostic image. The image composition unit 13 corresponds to the image composition means of the present invention.

  The long image P3 generated by stitching the strip images P1 is more suitable for diagnosis than an image photographed without stitching. The reason for this will be described. The strip image P1 is generated by allowing the subject to transmit an X-ray beam whose spread is restricted in the body axis direction A by the collimator 3a as indicated by a broken line in FIG. Consider the distortion of the subject image in the strip image P1 generated at this time. The left side of FIG. 8 represents a commonly performed fluoroscopic imaging. The X-ray beam irradiated from the X-ray tube 3 spreads greatly, passes through the subject, and enters the entire surface of the FPD 4. Since the X-ray beam spreads radially from the focal point in the X-ray tube 3 toward the FPD 4, the image of the subject M reaches the FPD 4 with the width expanded. That is, the image of the subject in the range of the solid arrow on the left side of FIG. 8 is enlarged to the range of the dashed arrow when reaching the FPD 4. Thus, when an image is taken with an X-ray beam that spreads radially, the image is greatly enlarged and distorted.

  The right side of FIG. 8 represents photographing of the strip image P1 according to the second embodiment. The X-ray beam irradiated from the X-ray tube 3 is limited in its spread by the collimator 3 a, passes through the subject, and enters a part of the FPD 4. Since the spread of the X-ray beam is suppressed, the image of the subject M reaches the FPD 4 without being widened so much. In this way, when the strip image P1 is captured while suppressing the spread of the X-ray beam, the expansion of the image is suppressed and the distortion of the image is suppressed.

  Thus, the strip image P1 has little image distortion and is suitable for obtaining the length and area of the fluoroscopic image of the subject. However, since the strip image P1 is an image in which the spread of the X-ray beam is suppressed, only a small part of the subject is imaged with a narrow field of view. Therefore, according to the configuration of the second embodiment, the strip image P1 is captured a plurality of times while the X-ray tube 3 and the FPD 4 are moved with respect to the subject. That is, a plurality of strip images P1 having different imaging positions are connected to obtain a long image P3 in which the entire image of the subject is reflected.

  Moreover, if the strip images P1 are connected to generate the long image P3, the amount of scattered X-rays generated inside the subject in each imaging can be suppressed. A clear image can be obtained without being disturbed.

  The shooting of the strip image P1 will be described. The left side of FIG. 9 shows a state where the strip image P1 is captured. As shown in FIG. 9, the strip images P1 are continuously shot while the X-ray tube 3 and the FPD 4 move in the body axis direction A with respect to the subject while maintaining the relative positions thereof. At this time, the X-ray beam irradiated from the X-ray tube 3 is collimated by the collimator 3 a, so that the spread in the body axis direction A is limited and reaches the FPD 4. That is, X-rays reach the area indicated by the thick frame on the right side of FIG. The image generation unit 11 generates an image for a portion indicated by a thick frame in the FPD 4, generates a strip image P <b> 1 having the same shape as the thick frame, and sends it to the image composition unit 13.

  Each time the strip image P1 is generated, the image composition unit 13 arranges the strip images P1 acquired up to the present in the body axis direction A and joins them together to generate a composite image P2. The generated composite image P2 is sent to the array display unit 25. The array display unit 25 displays the composite image P2.

  FIG. 10 shows a state where the array display unit 25 displays the composite image P2. The array display unit 25 displays a composite image P2 in which the strip images P1a to P1d acquired up to now are connected. The composite image P2 is updated every time the strip image P1 is acquired. Therefore, when the strip images P1 are sequentially photographed, the strip image P1a is displayed on the array display unit 25 at the stage of obtaining the first strip image P1a. Then, at the stage of obtaining the second strip image P1b, the combined image P2 in which the strip images P1a and P1b are joined is displayed on the array display unit 25. Thereafter, similarly, when the strip image P1a is generated, the image composition unit 13 joins the strip image P1a generated first to the strip image P1 generated this time in the order in which they were generated (captured). A composite image P2 is generated and displayed on the array display unit 25. That is, each time a new strip image P1 is generated, the array display unit 25 displays the image generated this time and the previously generated image side by side.

  In FIG. 10, there is a positional shift in the subject image between the strip image P1c and the strip image P1d. This deviation is caused by the subject moving during the imaging of both images P1c and P1d. The operator can give an instruction to interrupt the imaging of the strip image P1 through the console 26 at the time when the displacement of the subject during imaging is recognized.

<Operation of X-ray imaging apparatus>
Next, the operation of the X-ray imaging apparatus will be described with reference to FIG. In the long photographing operation, first, the subject M is placed on the top 2 (placement step T1), and the operator starts photographing the strip image P1 through the console 26 (imaging start step T2). Then, a composite image P2 is generated before photographing of the strip image P1 is completed, and this is displayed on the array display unit 25 (composite image display start step T3). After photographing of the strip image P1 is completed, all the strip images P1 are displayed. The long image P3 is generated by joining together and displayed on the array display unit 25 (long image display step T4). Hereinafter, these steps will be described in order.

<Installation step T1, shooting start step T2>
First, the subject M is placed on the top 2. When the surgeon gives an instruction to start photographing the strip image P <b> 1 through the console 26, the console 26 sends the instruction to the X-ray tube controller 6. The X-ray tube control unit 6 reads out the imaging conditions stored in the storage unit 28 and causes the X-ray tube 3 to start X-ray irradiation based on the imaging conditions. The console 26 also sends the operator's instructions to the X-ray tube movement control unit 8 and the FPD movement control unit 10. Along with this, the X-ray tube 3 and the FPD 4 start moving in the body axis direction A of the subject while maintaining their relative values.

<Composite image display start step T3>
An X-ray beam is emitted from the X-ray tube 3 toward the subject at a time interval. This X-ray irradiation is a single pulse irradiation performed under the same irradiation conditions as the first imaging. The image generator 11 generates a strip image P1 each time an X-ray beam is irradiated. The strip image P1 is sent to the image composition unit 13 every time it is generated. Since the strip image P1 is photographed a plurality of times while the X-ray tube 3 and the FPD 4 move in the body axis direction A of the subject, the portions of the subject to which each of the strip images P1 is photographed are different from each other. . Each time the strip image P1 is sent, the image composition unit 13 arranges the strip image P1 generated this time and the previously generated strip image P1 in the body axis direction A in the order in which they were generated (photographed). A composite image P2 is generated. The generated composite image P2 is sent to the array display unit 25. The array display unit 25 displays the composite image P2 (see FIG. 10). The composite image P2 displayed on the array display unit 25 is updated every time the strip image P1 is generated.

  At this time, the surgeon can visually recognize the composite image P2 and know whether the subject is being photographed smoothly. When the image of the subject is shifted in the middle as shown in FIG. 10, the operator can immediately stop the imaging. However, it is assumed that there is no problem in shooting in the subsequent operation description.

<Long image display step T4>
When the photographing of the series of strip images P1 is completed, the image composition unit 13 connects the first strip image P1 generated to the last strip image P1 generated in order of generation (photographing) and joins them together. An image P3 is generated and sent to the array display unit 25. The array display unit 25 displays the long image P3. The surgeon can visually check the displayed long image P3 and diagnose the subject.

  As described above, the above-described configuration includes the array display unit 25 that displays a plurality of strip images P1 at different shooting points in time. The display of the array display unit 25 is performed every time the strip image P1 is generated, and the strip image P1 generated this time and the previously generated strip image P1 are displayed side by side. By adopting such a configuration, it is possible to provide an X-ray imaging apparatus with reduced operability and excellent operability.

  In other words, the surgeon captures a plurality of strip images P1 and compares the strip images P1 displayed side by side when capturing the long image P3 in which the strip images P1 are connected to each other. I can know. According to the conventional configuration, the strip image joining process is performed when a series of photographing is completed. In the conventional configuration, the surgeon can only confirm the strip image that has been captured just before the strip image is captured. Therefore, even if the subject moves during the photographing of the strip image, the surgeon is not aware of the movement, and the image is not defective until the long image P3 displayed on the array display unit 25 is viewed after the photographing is completed. Recognizing the alignment, re-shooting. According to the present invention, the composite image P <b> 2 in which the images are joined between a series of image captures is displayed on the array display unit 25. Therefore, the operator can quickly notice the movement of the subject and can immediately stop the imaging. As described above, the X-ray imaging apparatus of the present invention is excellent in operability by reducing the labor of imaging.

  In addition, since the long image P3 is obtained after shooting in the conventional configuration, it is impossible to accurately know what long image P3 is acquired during shooting. Therefore, according to the conventional configuration, the shooting range of the long image P3 is set in advance wider than the range required for diagnosis, and shooting is started. Then, the X-ray irradiation range in the subject extends to a range that does not require imaging. Such a configuration is not desirable in the sense of reducing the amount of X-ray irradiation of the subject.

  According to the present invention, it is possible to visually recognize how the subject is seen through by photographing before the long image P3 is generated. Can do. When the surgeon recognizes that the shooting range of the long image P3 is excessive or insufficient during shooting, the operator can instruct to stop or continue shooting the strip image P1 through the console 26.

  The present invention is not limited to the above-described configuration and can be modified as follows.

  (1) In each of the embodiments described above, when an image is shot, the currently shot image and the first shot image are displayed side by side on the array display unit 25. It is not restricted to such a configuration. That is, the array display unit 25 may display the displayed images by removing the images from the oldest one. FIG. 12 shows how the array display unit 25 displays the strip image P1 in accordance with the operation described in the second embodiment. As can be seen from FIG. 12, even if the strip image P1 is generated in the future, the array display unit 25 has no more margin for displaying the new strip image P1. That is, the array display unit 25 can display four strip images P1.

  Therefore, according to this modification, when the number of strip images P1 acquired so far exceeds 4, the image composition unit 13 generates the composite image P2 by excluding the strip image P1a generated first, Thereafter, every time the strip image P1a is generated, four strip images P1a are selected from the most recently generated ones, and the composite image P2 is generated from them. In FIG. 13, the image composition unit 13 excludes the strip image P1a and generates a composite image P2 including the strip image P1e generated this time. The composite image P2 is displayed on the array display unit 25 as shown in FIG. Thus, the surgeon can surely know whether or not the shooting of the strip image P1 is smooth.

  The configuration of this modified example is that when the number of images generated by the image composition unit 13 exceeds the predetermined number indicating the number of images that can be displayed on the array display unit 25, a predetermined number of images are selected from the most recently generated images. Are combined to generate a composite image P2. In this way, it is possible to avoid a situation in which recently captured images are not displayed on the array display unit 25 and are not displayed. Such an image updating method can also be applied to the X-ray imaging apparatus 1 according to the first embodiment.

  (2) According to the second embodiment described above, the X-ray tube 3 and the FPD 4 are moved while maintaining their relative positions during imaging, but the present invention is not limited to this configuration. That is, the strip image P1 may be captured while only the X-ray tube 3 is moved, or the strip image P1 may be captured by changing the moving speed of the X-ray tube 3 and the FPD 4.

  (3) According to the first embodiment described above, imaging of the esophagus of the subject is performed. However, the present invention is not limited to the configuration described above, and imaging may be performed for other parts of the subject. .

  (4) Although the embodiment described above is a medical device, the present invention can also be applied to industrial and nuclear devices.

  (5) X-rays referred to in the above-described embodiments are an example of radiation in the present invention. Therefore, the present invention can be applied to radiation other than X-rays.

P2 Composite image 3 X-ray tube (radiation source)
4 FPD (detection means)
6 X-ray tube control unit (radiation source control means)
7 X-ray tube moving mechanism (radiation source moving means)
8 X-ray tube movement control unit (radiation source movement control means)
9 FPD moving mechanism (detector moving means)
10 FPD movement control unit (detector movement control means)
11 Image generation unit (image generation means)
12 Image adjustment unit (image adjustment means)
13 Image composition section (image composition means)
25 Array display section (array display means)
25a Display section (display means)
26 Console (input means)

Claims (6)

A radiation source that emits radiation;
Detection means for detecting radiation;
Image generating means for generating a plurality of images at different photographing points based on detection signals output one after another by the radiation source continuously emitting radiation;
Array display means for displaying the image generated this time and the previously generated image side by side each time an image is generated,
(A) input means for inputting an operator's instruction regarding adjustment of the images displayed on the array display means;
(B) an image adjusting unit that performs an image adjustment process on one of the images displayed on the array display unit based on the input of the input unit, and sends the image after the adjustment process to the array display unit; Prepared ,
Said image adjustment means, according to an instruction of the operator entered after each shot image, the radiographic apparatus, characterized that you execute the adjustment processing of the image in between shooting. The radiographic apparatus according to claim 1,
A radiation imaging apparatus, characterized in that a display means for displaying a single image and updating the image each time an image is taken is provided separately from the array display means. A radiation source that emits radiation;
Detection means for detecting radiation;
Image generating means for generating a plurality of images at different photographing points based on detection signals output one after another by the radiation source continuously emitting radiation;
Array display means for displaying the image generated this time and the previously generated image side by side each time an image is generated,
(C) radiation source moving means for moving the radiation source relative to the subject;
(D) radiation source movement control means for controlling the radiation source movement means;
(E) generating a composite image by stitching each of the elongated images in the direction perpendicular to the moving direction of the radiation source taken while the radiation source is moved with respect to the subject; Image combining means for displaying a plurality of images generated by the image generation means by displaying the composite image on a display means and displaying the images on the array display means ;
The image synthesizing means, a radiation imaging apparatus which is characterized that you generate the composite image by joining side by side in order of the generated to the current generated image from first generated image. The radiographic apparatus according to claim 3,
Detector moving means for moving the detection means relative to the subject;
Detector movement control means for controlling the detector movement means,
The radiation imaging apparatus, wherein the radiation source and the detection means are moved with respect to the subject while maintaining a relative position to each other. The radiographic apparatus according to claim 3 or 4,
When the generated image exceeds a predetermined number indicating the number of images that can be displayed on the array display unit, the image combining unit generates the combined image by excluding the elongated image generated first, and thereafter the image A radiographic apparatus characterized by selecting a predetermined number of images from the most recently generated image each time the image is generated and connecting them to generate the composite image. The radiographic apparatus according to any one of claims 1 to 5 ,
Radiation source control means for giving instructions of irradiation conditions to the radiation source,
A radiation imaging apparatus, wherein the radiation source continuously emits radiation under the same irradiation condition when generating a plurality of images.

Images