JP2013022041A - Radiographic apparatus for breast examination - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiographic apparatus for breast examination, capable of surely acquiring tomographic images by surely inserting the breast to a detector ring.SOLUTION: An opening of a gantry 11 is provided with a sensor 5 for detecting the insertion depth of the breast B and a distance display part for notifying the breast depth. Thus, an operator recognizes the insertion situation of the breast B when inserting the breast B to the opening of the gantry 11. Thus, the radiographic apparatus for a breast examination capable of surely acquiring tomographic images P by surely inserting the breast B to the detector ring 12 is provided.

Description

  The present invention relates to a radiographic apparatus for breast screening that detects a pair of annihilation radiations emitted from a subject and images a radiopharmaceutical distribution in the subject, and in particular, radiography for breast screening for cancer screening. Relates to the device.

  In medical institutions, radiation tomography apparatuses that image the distribution of radiopharmaceuticals are deployed. A specific configuration of such a radiation tomography apparatus will be described. A conventional radiation tomography apparatus includes a detector ring in which radiation detectors that detect radiation are arranged in an annular shape. This detector ring detects a pair of radiations (annihilation radiation pairs) in opposite directions that are irradiated from the radiopharmaceutical in the subject.

  One type of such a radiation tomography apparatus is a radiation tomography apparatus for breast examination. This radiographic apparatus for breast examination will be specifically described. FIG. 13 is a diagram for explaining a conventional radiographic apparatus for breast examination. In the conventional radiation imaging apparatus 51 for breast examination, one side of the breast B of the subject M is inserted into the detector ring 62 during the examination. In this state, the detector ring 62 detects the annihilation radiation pair irradiated from the subject M.

  The detector ring 62 identifies the source of the annihilation radiation pair emitted from the breast B, and a radiopharmaceutical distribution is generated based on this position information. Since radiopharmaceuticals have the property of accumulating more in cancer tissues than in normal tissues, breast cancer screening can be performed by diagnosing the distribution map of radiopharmaceuticals (see, for example, Patent Document 1 and Patent Document 2).

JP 2009-183448 A JP 2009-254787 A

However, the conventional configuration has the following problems.
That is, according to the conventional configuration, there is a problem that it is impossible to obtain a guarantee that the breast is properly inserted into the detector ring.

  The breast B is flexible and does not have a fixed shape. When the breast B is inserted into the detector ring 62, the breast B hits the gantry 61 and is deformed. Then, there is a possibility that tomographic imaging starts in a state where the breast B does not fit well in the detector ring 62.

  The surgeon cannot confirm the appearance of the breast B when inserting the breast B into the detector ring 62. This is because the gantry 61 surrounding the breast B becomes an obstacle to confirmation. Therefore, the surgeon cannot confirm whether the breast B is reliably inserted in the stage before the start of imaging.

  Then, it may happen that imaging is started without the breast B being inserted into the detector ring 62 successfully. In this case, the operator notices that the breast B could not be inserted only after visually confirming the tomographic image obtained after the end of imaging. In this case, the only way to obtain an image that can be used for diagnosis is to re-acquire the tomographic image.

  When the tomographic image is taken again, imaging is started again after the breast B is inserted deep in the detector ring 62. However, even in this process, there is no guarantee that the breast B is securely inserted into the detector ring 62.

  That is, according to the conventional configuration, imaging is repeated until a tomographic image suitable for diagnosis can be acquired. Such a phenomenon that the breast B does not fit into the detector ring 62 is particularly likely to occur particularly when the breast B to be examined is large.

  The present invention has been made in view of such circumstances, and an object of the present invention is to provide a radiographic apparatus for breast examination that can reliably acquire a tomographic image by inserting a breast into a detector ring. It is to provide.

The present invention has the following configuration in order to solve the above-described problems.
That is, the radiation imaging apparatus for breast examination according to the present invention detects and detects the gantry having an opening for inserting the breast of the subject and the insertion depth of the breast of the subject provided in the opening of the gantry. It is characterized by comprising a sensor for outputting a signal and a depth notifying means for notifying the insertion depth of the breast based on the detection signal of the sensor.

  [Operation and Effect] According to the configuration of the present invention, the sensor for detecting the insertion depth of the breast in the opening of the gantry and the notification means for notifying the breast depth are provided. Thereby, the operator can know the insertion state of the breast when inserting the breast into the opening of the gantry. Accordingly, it is possible to provide a radiation imaging apparatus for breast examination that can reliably acquire a tomographic image by reliably inserting a breast into a detector ring.

  In the above radiographic apparatus for breast examination, it is more preferable that the sensor sends a detection signal to the depth notifying unit in real time, and the depth notifying unit updates and notifies the insertion depth of the breast at the real time.

  [Operation / Effect] The above-described configuration shows a more specific configuration of the photographing apparatus of the present invention. If the breast insertion depth is updated and notified in real time, the current state of the breast insertion depth can be known, so that the breast can be reliably inserted into the detector ring.

  Further, in the above radiographic apparatus for breast examination, when the breast is inserted into the opening, update notification means for notifying that the insertion depth of the breast has become shallow based on the detection signal of the sensor is provided. desirable.

  [Operation / Effect] The above-described configuration shows a more specific configuration of the photographing apparatus of the present invention. If the insertion depth of the breast informs that the insertion depth of the breast has become shallow, the operator can quickly know that the subject has moved and the breast has been misaligned after inserting the breast. be able to. Further, the operator can easily recognize whether or not the breast insertion depth is maximum when adjusting the positional relationship between the gantry and the breast for the purpose of increasing the breast insertion depth.

  In the above-described radiation imaging apparatus for breast examination, it is more desirable that the sensor is provided at one end of the gantry opening opposite to the side where the breast is inserted.

  [Operation / Effect] The above-described configuration shows a more specific configuration of the photographing apparatus of the present invention. If the sensor is provided at one end of the gantry opening opposite to the side where the breast is inserted, the insertion depth of the breast can be detected more reliably.

  Further, the above-described radiation imaging apparatus for breast examination may include a gantry moving means for moving the gantry relative to the subject in a direction orthogonal to the breast insertion direction, and a gantry movement control means for controlling the gantry moving means. More desirable.

  [Operation / Effect] The above-described configuration shows a more specific configuration of the photographing apparatus of the present invention. If a mechanism for adjusting the positional relationship between the breast and the gantry is provided by moving the gantry relative to the subject in a direction orthogonal to the breast insertion direction, the breast position adjustment can be made simpler.

  In the above radiographic apparatus for breast examination, it is more preferable that the radiation detector for detecting radiation is provided in the gantry with a detector ring arranged in an arc shape to image a radiopharmaceutical distributed in the breast.

  [Operation / Effect] The above-described configuration shows a more specific configuration of the photographing apparatus of the present invention. The positron emission tomography apparatus requires time for imaging. Therefore, re-imaging in such an apparatus places a heavy burden on the subject, so it is necessary to insert the breast securely before imaging. If the present invention is applied to a positron emission tomography apparatus, the breast can be reliably introduced into the detector ring, so that the imaging is reliable.

  Further, the above-described radiographic apparatus for breast examination includes a radiation source that irradiates radiation inside the gantry and a radiation detector that detects radiation, and performs imaging by transmitting radiation emitted from the radiation source to the breast. For example, it is more desirable.

  [Operation / Effect] The above-described configuration shows a more specific configuration of the photographing apparatus of the present invention. In the apparatus as described above, the amount of radiation emitted to the subject must be reduced as much as possible. Therefore, in such an apparatus, it is not desirable to perform the imaging again in consideration of the safety of the subject. Therefore, it is necessary to reliably insert the breast at the time of imaging. If the present invention is applied to the above-described configuration, the breast can be surely introduced into the gantry, so that photographing is safe.

  According to the configuration of the present invention, the sensor includes a sensor that detects the insertion depth of the breast in the opening of the gantry and a notification unit that notifies the breast depth. Thereby, the operator can know the insertion state of the breast when inserting the breast into the opening of the gantry. Accordingly, it is possible to provide a radiation imaging apparatus for breast examination that can reliably acquire a tomographic image by reliably inserting a breast into a detector ring.

1 is a functional block diagram illustrating a configuration of a radiation tomography apparatus according to Embodiment 1. FIG. FIG. 3 is a plan view illustrating the configuration of the console according to the first embodiment. 6 is a schematic diagram for explaining detection of a breast insertion depth according to Embodiment 1. FIG. 6 is a schematic diagram for explaining detection of a breast insertion depth according to Embodiment 1. FIG. 6 is a schematic diagram for explaining detection of a breast insertion depth according to Embodiment 1. FIG. 6 is a schematic diagram for explaining detection of a breast insertion depth according to Embodiment 1. FIG. 1 is a perspective view illustrating a configuration of a radiation detector according to Embodiment 1. FIG. FIG. 3 is a functional block diagram for explaining the operation of the radiation tomography apparatus according to Embodiment 1. It is a functional block diagram explaining the whole structure of the X-ray tomography apparatus which concerns on Example 2. FIG. FIG. 10 is a schematic diagram for explaining the operation of the X-ray tomography apparatus according to Embodiment 2. It is sectional drawing explaining the structure of one modification of this invention. It is sectional drawing explaining the structure of one modification of this invention. It is sectional drawing explaining the structure of the radiography apparatus of a conventional structure.

  Embodiments of a radiation tomography apparatus according to the present invention will be described below with reference to the drawings. The gamma rays in Example 1 are an example of the radiation of the present invention. The configuration of the first embodiment is a mammography apparatus for breast examination. That is, the radiation tomography apparatus according to the first embodiment performs imaging of a radiopharmaceutical distributed in the breast B to generate a tomographic image.

<Overall configuration of radiation tomography apparatus>
FIG. 1 is a functional block diagram illustrating a specific configuration of the radiation tomography apparatus according to the first embodiment. The radiation tomography apparatus 9 according to the first embodiment includes a gantry 11 having an opening for inserting the breast B of the subject M from the z direction, and the breast B of the subject M provided inside the gantry 11 in the z direction. And a ring-shaped detector ring 12 to be inserted. The opening provided in the detector ring 12 has a cylindrical shape (exactly, a regular octagonal prism) extending in the z direction. Therefore, the detector ring 12 itself extends in the z direction. Note that the area of the opening of the detector ring 12 is an imaging field in which a tomographic image P of the radiation tomography apparatus 9 can be generated. The z direction is along the direction in which the central axis of the detector ring 12 extends.

  The top plate 10 is provided for the purpose of placing the subject M in a stomach-like state. The top plate 10 is provided with a hole through which the breast B of the subject M is inserted in the z direction. The breast B is inserted into the detector ring 12 through the hole. The opening of the gantry 11 is provided vertically upward, and the breast B is inserted into this opening from the vertically downward direction.

  The gantry 11 is placed on the support base 25. The support base 25 is located on the back side of the gantry 11 when viewed from the subject M. The support base 25 can reciprocate in the longitudinal direction of the top plate 10 as indicated by arrows in FIG. The longitudinal direction of the top plate 10 is orthogonal to the insertion direction of the breast B inserted into the gantry 11. Then, the gantry 11 and the sensor 5 described later also move following the support base 25. On the other hand, since the top plate 10 does not follow the movement of the support base 25 and does not move, the relative position between the gantry 11 and the breast B can be adjusted by moving the support base 25. The movement of the support base 25 is realized by the support base movement mechanism 23. The support base movement control unit 24 controls the support base movement mechanism 23. The support base movement mechanism 23 corresponds to the gantry movement means of the present invention, and the support base movement control unit 24 corresponds to the gantry movement control means of the present invention.

  A sensor 5 for detecting the insertion depth of the breast B is provided on the support surface on which the gantry 11 is placed in the support base 25. The sensor 5 is provided inside the opening of the gantry 11. Therefore, the sensor 5 is provided at one end of the opening of the gantry 11 opposite to the side where the breast B is inserted. The sensor 5 can output a detection signal in real time. As a specific example of the sensor 5, an infrared sensor can be employed.

  The console 35 is used to input various operations performed by the operator on the radiation tomography apparatus 9. As shown in FIG. 2, the console 35 includes a distance display unit 35a for notifying the insertion depth of the breast B of the subject M in millimeters, a lamp 35b for notifying the update of the insertion depth, and a distance display. A reset button 35c for resetting a value displayed in the section 35a. Detection signals are sent from the sensor 5 to the distance display unit 35a and the lamp 35b in real time. The distance display unit 35a and the lamp 35b are configured to change the display based on this detection signal. The surgeon inserts the gantry 11 into the breast B while confirming the display of the distance display part 35a and the lamp 35b. The distance display unit 35a corresponds to the depth notification unit of the present invention, and the lamp 35b corresponds to the update notification unit of the present invention.

<Operations of Distance Display Unit 35a and Lamp 36b During Breast Insertion>
3-6 is a figure explaining operation | movement of the distance display part 35a and the lamp | ramp 35b. In this description of the operation, it is assumed that the breast B to be examined is being inserted into the opening of the gantry 11.

  FIG. 3 shows an initial state before the breast B is inserted into the opening. At this time, the display of the distance display part 35a is an initial value of 100 mm. The initial value of the distance display part 35a is preferably set longer than the length of the opening in the z direction. On the other hand, the lamp 35b is not lit.

  FIG. 4 shows a state in which the breast B has started to be inserted into the opening. When the surgeon inputs an instruction to start breast insertion through the console 35, the sensor 5 starts infrared irradiation in the vertically upward direction. In this state, the breast B is inserted into the opening from the vertically downward direction. The sensor 5 detects an infrared ray that is reflected by the breast B and returns, and outputs a detection signal indicating a distance d between the sensor itself and the breast B that reflects the infrared ray. This distance d represents the insertion depth of the breast B. The sensor 5 sends a detection signal to the distance display part 35a and the lamp 35b. The distance display unit 35a displays the distance d in real time. On the other hand, the lamp 35b starts to light.

  FIG. 5 shows a state where the breast B has been inserted into the opening. The distance display part 35a displays the minimum distance since the breast B has been inserted. Further, the lamp 35b continues to be lit. The lighting of the lamp 35b is continued during a period in which the distance d is shorter. That is, the lamp 35b notifies the surgeon that the insertion depth of the breast B has been changed to be deeper.

  The lamp 35b continues to be lit even when the breast B is completely inserted and does not move with respect to the gantry 11. Thereby, the lamp 35b notifies the operator that the state where the breast B is inserted deeply is maintained.

  FIG. 6 shows a case where the subject M has moved after the state of FIG. 5 in which the breast B has been inserted into the opening. As a result, it is assumed that the breast B is partially pulled out from the opening of the gantry 11. The distance display unit 35a displays a distance longer than the previous one and notifies the surgeon that the positional deviation of the breast B has occurred. Similarly, the lamp 35b stops lighting when the distance d becomes longer, and notifies the operator that the insertion depth of the breast has become shallow due to the positional deviation of the breast B.

  On the other hand, the reset button 35c is provided for the purpose of resetting the distance display (see FIG. 2). When the reset button 35c is pressed, the distance display unit 35a and the lamp 35b return to the initial state described with reference to FIG.

  The shielding plate 13 is made of tungsten, lead, or the like (see FIG. 1). Since the radiopharmaceutical is also present in a portion other than the breast B of the subject M, an annihilation γ-ray pair is also generated therefrom. When an annihilation gamma ray pair generated from a part other than such a region of interest enters the detector ring 12, it interferes with tomographic imaging. Therefore, a ring-shaped shielding plate 13 is provided so as to cover one end of the detector ring 12 on the side close to the subject M in the z direction.

  The clock 19 sends time information as a serial number to the detector ring 12. The detection signal output from the detector ring 12 is given time information indicating when the γ-ray is detected, and is input to the filter unit 20 described later.

  The configuration of the detector ring 12 will be described. The detector ring 12 is formed by arranging eight radiation detectors 1 in a virtual circle on a plane perpendicular to the z direction (center axis direction) to form one unit ring. Three unit rings are arranged in the z direction to form a detector ring 12.

  The configuration of the radiation detector 1 will be briefly described. FIG. 7 is a perspective view illustrating the configuration of the radiation detector according to the first embodiment. As shown in FIG. 7, the radiation detector 1 includes a scintillator 2 that converts radiation into light, and a photodetector 3 that includes a photomultiplier tube that detects light. A light guide 4 for transmitting and receiving light is provided at a position where the scintillator 2 and the photodetector 3 are interposed.

The scintillator 2 is configured by scintillator crystals arranged three-dimensionally. The scintillator crystal is composed of Lu _{2 (1-X)} Y _2X SiO ₅ (hereinafter referred to as LYSO ₎ in which Ce is diffused. The light detector 3 can specify the light generation position of which scintillator crystal emits light, and also specifies the light intensity and the time when the light is generated. Can do. The scintillator 2 having the configuration of the first embodiment is merely an example of an aspect that can be adopted. Therefore, the configuration of the present invention is not limited to this.

  The coincidence counting unit 21 (see FIG. 1) receives a detection signal output from the detector ring 12 via a filter unit 20 described later. The two gamma rays simultaneously incident on the detector ring 12 are annihilation gamma ray pairs caused by the radiopharmaceutical in the subject. The coincidence counting unit 21 counts the number of times that an annihilation γ-ray pair is detected for every two combinations of scintillator crystals constituting the detector ring 12, and sends the result to the tomographic image generation unit 22. The coincidence of the detection signals by the coincidence unit 21 uses time information given to the detection signals by the clock 19.

  The filter unit 20 is provided for the purpose of preventing unnecessary data in the detector ring 12 from being sent to the coincidence unit 21. The filter unit 20 can thin out the detection signal so as to reduce the load on the coincidence counting unit 21.

  The tomographic image generation unit 22 generates a tomographic image P when the opening of the detector ring 12 is cut along a certain plane based on the coincidence counting data output from the coincidence counting unit 21.

  The display unit 36 displays the tomographic image P generated by the tomographic image generation unit 22. The storage unit 37 stores all of the detection signal output from the detector ring 12, the coincidence counting data generated by the coincidence counting unit 21, the data generated by the operation of each unit such as the tomographic image P, and the parameters referred to in the operation of each unit. It is something to remember.

  The radiation tomography apparatus 9 includes a main control unit 41 that comprehensively controls each unit. The main control unit 41 is constituted by a CPU, and realizes the units 19, 20, 21, 22, and 24 by executing various programs. In addition, each above-mentioned part may be divided | segmented and implement | achieved by the control apparatus which takes charge of them.

<Operation of radiation tomography system>
Next, the operation of the radiation tomography apparatus will be described with reference to FIG. In order to examine breast B with the radiation tomography apparatus of Example 1, first, the subject M to which the radiopharmaceutical is administered is placed on the top 10 so as to become a stomach (subject placement step S1). At this time, since the surgeon inputs the start of breast insertion through the console 35, the distance display unit 35a and the lamp 35b have started display operation / lighting operation (see FIG. 4).

  When the insertion of the breast B is completed, the operator instructs the movement of the support base 25 through the console 35. As a result, the gantry 11 moves in the longitudinal direction of the top 10 with respect to the subject M, and the position of the gantry 11 relative to the subject M is adjusted (subject position adjustment step S2). The operator adjusts this position while confirming the distance display portion 35a and the lamp 35b. If the surgeon tries to insert the breast B deeper into the opening and moves the support base 25 too far in one direction to the subject M, the distance display part 35a and the lamp 35b will make the insertion depth of the breast B shallower. Notify the surgeon The surgeon can return the insertion depth of the breast B to the original state by moving the support base 25 in the reverse direction in accordance with this notification.

  When the operator completes the position adjustment of the subject M and the operator instructs the start of tomographic imaging through the console 35, the detector ring 12 starts detecting the disappeared γ-ray pair (imaging start step S3). The tomographic image generation unit 22 generates a tomographic image P by imaging the detected annihilation gamma ray pair. The tomographic image P is displayed on the display unit 36, and the operation of the radiation tomography apparatus in Embodiment 1 is completed.

  As described above, according to the configuration of the present invention, the sensor 5 that detects the insertion depth of the breast B and the distance display unit 35 a that notifies the breast depth are provided in the opening of the gantry 11. Thereby, the operator can know the insertion state of the breast B when inserting the breast B into the opening of the gantry 11. As a result, it is possible to provide a radiation imaging apparatus for breast examination that can reliably acquire a tomographic image by reliably inserting the breast B into the detector ring 12.

  Further, if the breast insertion depth is updated and notified in real time as described above, the current state of the insertion depth of the breast B can be known, so that the breast B can be surely inserted into the detector ring 12. Can do.

  Moreover, if the structure which notifies that the insertion depth of the breast B has become deeper like the above-mentioned lamp 35b is provided, after the operator inserts the breast B, the subject M moves and the breast B Can quickly know that the position has shifted. In addition, when adjusting the positional relationship between the gantry 11 and the breast B for the purpose of increasing the insertion depth of the breast B, the operator can easily recognize whether the insertion depth of the breast B is maximum. Can do.

  As described above, if the sensor 5 is provided at one end of the opening of the gantry 11 opposite to the side where the breast B is inserted, the insertion depth of the breast B can be detected more reliably.

  Then, if the gantry 11 is moved relative to the subject M in a direction orthogonal to the insertion direction of the breast B to provide a mechanism for adjusting the positional relationship between the breast B and the gantry 11, the position of the breast B is adjusted. It can be made simpler.

  The electron emission tomography apparatus requires time for imaging. Therefore, since the burden on the subject M is heavy when re-imaging is performed in such an apparatus, it is necessary to reliably insert the breast B before imaging. If the present invention is applied to a positron emission tomography apparatus, the breast B can be reliably introduced into the detector ring 12, so that imaging is assured.

  Subsequently, another aspect 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. The X-ray tomography apparatus of the present invention is for breast examination. The X-ray tomography apparatus according to the second embodiment has a configuration in which X-rays emitted from an X-ray tube are transmitted through a breast B and imaged, and an object M in a sitting position is imaged.

<Overall configuration of X-ray tomography apparatus>
First, the overall configuration of the X-ray tomography apparatus 29 according to the second embodiment will be described. The radiation tomography apparatus according to Embodiment 2 includes a gantry 11 having an opening for inserting the breast B of the subject M from the z direction as shown in FIG. The manner in which the breast B is inserted into the opening of the gantry 11 is the same as that of the first embodiment (see FIGS. 2 to 6). However, since the X-ray tomography apparatus 29 is an apparatus for diagnosing the subject M in the sitting position, the insertion direction of the breast B and the irradiation direction of infrared rays are horizontal.

  Inside the gantry 11, an X-ray tube 33 for irradiating X-rays and an FPD 34 for detecting X-rays are provided. X-rays irradiated from the X-ray tube 33 pass through the opening of the gantry 11 and reach the FPD 34. The X-ray tube 33 corresponds to the radiation source of the present invention, and the FPD 34 corresponds to the radiation detector of the present invention.

  A support plate 5 a that supports the sensor 5 is provided at one end of the opening of the gantry 11 opposite to the side where the breast B is inserted. The sensor 5 is supported by the support plate 5a. The sensor 5 can output a detection signal in real time. As a specific example of the sensor 5, an infrared sensor can be employed.

  The support column 25 a extends in the vertical direction and supports the gantry 11. The gantry moving mechanism 23a moves the gantry 11 in the vertical direction with respect to the support column 25a. This vertical direction is orthogonal to the insertion direction of the breast B inserted into the gantry 11. The gantry movement control unit 24a is provided for the purpose of controlling the gantry movement mechanism 23a. When the gantry 11 is moved relative to the support column 25a, the support plate 5a and the sensor 5 move following the gantry 11. The gantry movement mechanism 23a corresponds to the gantry movement means of the present invention, and the gantry movement control unit 24a corresponds to the gantry movement control means of the present invention.

  The X-ray tube control unit 6 is provided for the purpose of controlling the X-ray tube 33 with a predetermined tube current, tube voltage, and pulse width. The FPD 34 detects X-rays emitted from the X-ray tube 33 and transmitted through the subject M, and generates a detection signal. This detection signal is sent to the image generation unit 31, where a perspective image P0 in which a projection image of the subject M is reflected is generated. The tomographic image generation unit 32 generates a tomographic image P1 when the subject M is cut along an arbitrary tomographic plane based on the fluoroscopic image P0 generated by the image generation unit 31.

  The rotation of the X-ray tube 33 and the FPD 34 will be described. The X-ray tube 33 and the FPD 34 are integrally rotated around the central axis extending in the direction in which the opening of the gantry 11 into which the breast B is inserted is extended by the rotation mechanism 7. More specifically, the X-ray tube 33 and the FPD 34 are rotationally moved while maintaining a relative positional relationship with each other as shown in FIG. At this time, the X-ray tube 33 rotates while drawing the locus of the virtual circle VC centered on the center point on the line segment connecting the X-ray tube 33 and the FPD 34 by the rotation mechanism 7. A direction perpendicular to the virtual circle VC (paper surface penetration direction in FIG. 10: z direction) coincides with the extending direction of the opening of the gantry 11. The rotation control unit 8 is provided for the purpose of controlling the rotation mechanism 7.

  The display unit 36 is provided for the purpose of displaying a tomographic image P1 acquired by X-ray imaging. The console 35 is provided for the purpose of inputting an instruction such as an X-ray irradiation start by the operator. The main control unit 41 is provided for the purpose of comprehensively controlling each control unit. The main control unit 41 is constituted by a CPU, and realizes the control units 6 and 8 and the units 31 and 32 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 37 stores all parameters relating to control of the X-ray tomography apparatus 29 such as parameters used for imaging and intermediate images generated in accordance with image processing.

  Next, the operation of the X-ray tomography apparatus 29 will be described with reference to FIG. To examine breast B with the X-ray tomography apparatus 29 of the second embodiment, first, the breast B of the subject M to which the radiopharmaceutical is administered is inserted into the opening of the gantry 11 (subject placement step S1). . At this time, since the surgeon inputs the start of breast insertion through the console 35, the distance display unit 35a and the lamp 35b have started display operation / lighting operation (see FIG. 4).

  When the insertion of the breast B is completed, the operator instructs the movement of the gantry 11 through the console 35. Accordingly, the gantry 11 moves in the vertical direction with respect to the subject M, and the position of the gantry 11 with respect to the subject M is adjusted (subject position adjustment step S2). The operator adjusts this position while confirming the distance display portion 35a and the lamp 35b. If the surgeon tries to insert the breast B deeper into the opening and moves the gantry 11 to the subject M in one direction too much, the distance display part 35a and the lamp 35b cause the insertion depth of the breast B to become shallow. Notify the surgeon that he is. The surgeon can return the insertion depth of the breast B to the original state by moving the gantry 11 in the reverse direction in accordance with this notification.

  When the operator instructs the start of tomographic imaging through the console 35, the X-ray tube control unit 6 intermittently irradiates X-rays according to the irradiation time, tube current, and tube voltage stored in the storage unit 37. (Shooting start step S3). Meanwhile, the rotation mechanism 7 rotates the X-ray tube 33 and the FPD 34. The FPD 34 detects X-rays that have passed through the subject M among X-rays irradiated by the X-ray tube 33, and sends a detection signal at this time to the image generation unit 31.

  The image generation unit 31 converts the detection signal transmitted from the FPD 34 into an image, and generates a fluoroscopic image P0 in which the X-ray intensity is mapped. Since the FPD 34 sends a detection signal to the image generation unit 31 every time the X-ray tube 33 irradiates X-rays, the image generation unit 31 generates a plurality of fluoroscopic images P0. Each of the fluoroscopic images P0 includes an image of the breast B of the subject M having a different imaging direction.

  The fluoroscopic image P0 is sent to the tomographic image generation unit 32. The tomographic image generation unit 32 reconstructs a series of fluoroscopic images P0 having information related to the three-dimensional structure of the subject M by being photographed while changing the direction, and the subject having the body axis in the z direction. A tomographic image P1 in which the breast B of M is cut in a circle is generated. The tomographic image P1 is displayed on the display unit 36, and the operation of the X-ray tomography apparatus 29 in the second embodiment is completed.

  In the apparatus as described above, the amount of radiation emitted to the subject M must be reduced as much as possible. Therefore, in such an apparatus, it is not desirable to perform the imaging again in view of the safety of the subject M. Therefore, it is necessary to reliably insert the breast B at the time of imaging. If the present invention is applied to the above-described configuration, the breast B can be surely introduced into the gantry 11, so that photographing is safe.

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

  (1) Although the above-described first embodiment includes the mechanism for moving the support base 25 with respect to the subject M, the present invention is not limited to this configuration. The support 25 and the gantry 11 may be fixed to the top plate 10 and the alignment of the breast B of the subject M may be realized by moving the subject M on the top plate 10.

  (2) In the above-described embodiment, the sensor 5 is provided in the center of the opening of the gantry 11, but the present invention is not limited to this configuration. As shown in FIG. 11, a plurality of sensors 5 are provided in the opening of the gantry 11, and the distance display unit 35 a and the lamp 35 b operate based on a detection signal indicating the lowest distance among the detection signals output from the plurality of sensors 5. You may make it do.

  (3) Although the above-described first embodiment is a radiation tomography apparatus that causes the subject M to sit on the top 10, the present invention is not limited to this configuration. That is, as shown in FIG. 12, it may be configured to image the subject M in the sitting position.

  (4) In the above configuration, the present invention is applied to the positron emission tomography apparatus, but the present invention is not limited to this configuration. Instead of the positron emission tomography apparatus, a single photon ECT apparatus may be used. Further, the present invention may be applied to a positron emission tomography apparatus / single photon ECT apparatus having a flat panel detector, or to a nuclear magnetic resonance CT apparatus.

  (5) In the first embodiment described above, the detector ring 12 is an O-shaped ring, but may instead be a C-shaped arc.

5 Sensor 11 Gantry 12 Detector ring 23 Support base moving mechanism (gantry moving means)
24 Support stand movement control unit (gantry movement control means)
33 X-ray tube (radiation source)
34 FPD (radiation detector)
35a Distance display section (depth notification means)
35b lamp (update notification means)

Claims (7)

A gantry with an opening for inserting the breast of the subject;
A sensor that detects the insertion depth of the breast of the subject provided in the opening of the gantry and outputs a detection signal;
A radiation imaging apparatus for breast examination, comprising: a depth notifying unit for notifying the insertion depth of the breast based on a detection signal of the sensor. The radiation imaging apparatus for breast examination according to claim 1,
The sensor sends a detection signal to the depth notification means in real time,
The depth notifying means updates and notifies the insertion depth of the breast at a full time, and is a radiographic apparatus for breast examination. The radiation imaging apparatus for breast examination according to claim 2,
A radiographic apparatus for breast examination, comprising update notification means for notifying that the insertion depth of the breast has become shallow based on a detection signal of the sensor when the breast is inserted into the opening. The radiographic apparatus for breast examination according to any one of claims 1 to 3,
A radiation imaging apparatus for breast examination, wherein the sensor is provided at one end of the gantry opposite to the side where the breast is inserted in the opening. In the radiography apparatus for breast examination according to any one of claims 1 to 4,
Gantry moving means for moving the gantry relative to the subject in a direction perpendicular to the breast insertion direction;
A radiation imaging apparatus for breast examination, comprising: a gantry movement control means for controlling the gantry movement means. The radiographic apparatus for breast examination according to any one of claims 1 to 5,
A radiation detector for detecting radiation inside the gantry comprises a detector ring arranged in an arc,
A radiographic apparatus for breast examination, characterized by imaging a radiopharmaceutical distributed in the breast. The radiographic apparatus for breast examination according to any one of claims 1 to 5,
A radiation source for irradiating the inside of the gantry and a radiation detector for detecting the radiation;
A radiation imaging apparatus for breast examination, which performs imaging by transmitting radiation emitted from the radiation source to a breast.

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