JP3947152B2 - Mammography equipment - Google Patents

Description

The present invention relates to a mammography apparatus for examining a breast of a subject.

In the examination of mammography (X-ray mammography apparatus) using a screen / film combination mainly used at present, image diagnosis of mammography images (hereinafter referred to as mammogram images) in many hospitals includes, for example, the following It is done in the following procedure.

  First, a doctor in an examination request department (for example, mammary gland surgery) requests an examination of a patient (for example, examination by mammography) to the radiology department. This request is made by issuing an inspection request form. The examination request form includes the patient ID number, name, date of birth, gender, examination request department name, examination request doctor name, examination modality (here, mammography), site, method, examination purpose, clinical information Etc. are described.

  Next, a radiology examination engineer inspects the patient (takes a mammogram image by mammography) in accordance with the instructions in the examination request form, and develops the film.

  Then, a doctor who interprets images interprets the developed film. Interpretation means that a doctor sees an uninterpreted image, confirms a diagnosis, and completes an interpretation report. At this time, an image (film) of a past examination of the patient being examined is often referred to. It is important to use the images of past examinations for interpretation in order to improve the quality of interpretation. The doctor who performs interpretation interprets the diagnosis and creates an interpretation report. At this time, the information that the doctor performing the interpretation describes in the interpretation report includes the findings and conclusions obtained by reading the image, the name of the interpretation doctor, the date of interpretation, and the like. Then, the interpretation report is sent from the doctor who performed the interpretation to the doctor in the examination request department.

  As an imaging condition for mammography using a screen / film combination, characteristic X-rays using a Mo (Rh) target and a Mo (Rh) filter are effectively used for the purpose of improving image quality. The X-ray tube voltage is a low tube voltage of 30 kvp or less.

  Next, mammography inspection without using a screen / film combination will be described. Here, a mammography detection system using a computed radiography, a slot scan method, a two-dimensional CCD method, or the like will be described.

  Computed radiography (Computed-Radiography) is an X-ray imaging method that uses a plate (imaging plate, IP) coated with a photostimulable luminescent material instead of using a conventional film as an X-ray detector. The imaging plate has a very wide dynamic range compared to the film, and can take an image in a wide dose range. When the imaging plate is irradiated with X-rays, the energy level of electrons is increased by the energy of the X-rays, and the X-ray intensity distribution is stored as a latent image. When a high-order electron is excited by laser irradiation later, the energy at that time is detected as light. Since this light is proportional to the energy of the X-rays absorbed by the imaging plate, an X-ray image can be obtained electrically (for example, as a digital image).

  US Pat. No. 4,721,856 describes the use of such an imaging plate in a detection system for mammography.

  Current imaging plates have various problems. That is, the resolution is poor (pixel size of the pixel is 100 μm × 100 μm), there is a lot of noise, the IP is scratched when used, and the performance deteriorates (the IP needs to be used and replaced 100,000 times), There is a problem that the device is expensive.

  Next, a case where the slot scan method is used for the mammography detection system will be described. In the slot scanning method, a fan beam-shaped X-ray is irradiated to scan the breast. X-ray detection uses a detector using a linear CCD. At this time, the influence of scattering (scatter) is reduced by moving the detector in accordance with the scanning of the irradiated X-rays. Although it is a detector using a CCD, it is not a complete line detector but a semi-area detector having pixels in the width direction. In the semi-area detector, if scanning is performed in accordance with the CCD charge transfer speed in the width direction, the charges of the pixels are added by the width size, so that the load on the X-ray tube can be reduced.

  The detected X-rays are converted into light by an intensifying screen, which is guided to the CCD by a tapered fiber. For details, the following documents can be referred to.

Yaffe MJ et al: Imaging performance of a prototype scanned-slot digital mammography system, SPIE.Physics of Medical Imaging, 93-103 (1993). There are reports that it is appropriate to use a W target and set the X-ray tube voltage to 40 kvp, unlike the imaging conditions in the case of a screen / film combination. For details, the following documents can be referred to.

Yaffe M.J. et al: Dynamic range requirements in digital mammography, Medical Physics 20, 1621-1633 (1993) At present, the slot scan method has an advantage that an image with good image quality can be obtained. However, there are also disadvantages such as having mechanical elements and low device reliability and relatively expensive devices.

  Next, the case where the two-dimensional CCD system is used for the mammography detection system will be described. Examples of the digital detector using the two-dimensional CCD include the following. That is, there are II-TV, intensifying screen-lens-CCD, intensifying screen-tapered fiber-CCD digital detectors, and the like.

  The II-TV digital detector digitizes light multiplied by II (image intensifier) with a CCD TV camera.

  At present, there are problems such as (1) the resolution is low in a large field of view, (2) II is bulky and obstructs the shape, and (3) the apparatus is relatively expensive.

  The intensifying screen-lens-CCD digital detector receives light emitted from the intensifying screen with a lens and collects it on a CCD TV camera for digitization.

  At present, there are problems such as (1) low resolution in a large field of view and (2) low light quantity.

  An intensifying screen-tapered fiber-CCD digital detector guides the light emitted from the intensifying screen to the CCD with a tapered fiber for digitization.

  At present, there are problems that (1) the amount of light is small and (2) the device is relatively expensive.

  For the intensifying screen-lens-CCD and intensifying screen-tapered fiber-CCD digital detectors, reference can be made to the following papers. Roehrig H et al: Digital X-ray Cameras for Real-time Stereo tactic Breast Needle Biopsy, SPIE. Physics of Medical Imaging, 213-224 (1993) Detector that overcomes the problems of various detectors as described above There is a TFT flat detector (TFT).

  Next, a case where a TFT flat panel detector is used for a mammography detection system will be described.

  The TFT flat detector detects light emitted from the intensifying screen with a photodiode array. For details, you can refer to the following paper. Antonuk L.E. et al: Large area, Flat-Panel a-Si: H Arrays for X-ray Imaging, SPIE. Physics of Medical Imaging, 18-29 (1993) Next, computer-aided diagnosis (CAD) will be described.

  Taking advantage of the characteristics of digital images that are easy to process by a computer, attempts have been made to detect abnormalities by analyzing images using a computer. This technique is called computer-aided diagnosis (CAD) and is expected to be used for the purpose of improving the accuracy of image diagnosis and reducing the burden on doctors.

The abnormality detection algorithm is introduced in the following documents, for example. (1) Katsuragawa, S. et al: Image feature analysis and computer-aided diagnosis in digital radiography: Classification of normal and abnormal lungs with interstitial disease in chest images.Medical Physics 16,38-44 (1989)
(2) Giger, ML et al: Image feature analysis and computer-aided diagnosis in digital radiography: 3. Automated detection of nodules in peripheral lung fields.Medical Physics 15,158-166 (1988)
(3) Chan, HP et al: Image feature analysis and computer-aided diagnosis in digital radiography: 1. Automated detection of microcalcifications in mammography. Medical Physics 14,538-548 (1987) (4) Doi Kunio et al. Possibility of support diagnosis "Journal of Japanese Society of Radiological Technology, p653-663, 1989 The technology is also disclosed for a system for detecting abnormalities such as tumor shadows in 1989.

(1) Japanese Patent Application Laid-Open No. 02-185240 (2) Japanese Patent Application Laid-Open No. 02-152443 (3) Japanese Patent Application Laid-Open No. 01-125675 In particular, regarding CAD for breast cancer, US Pat. It describes how to identify whether the indicated cancer shadow is benign or malignant. U.S. Pat. No. 4,907,156 describes a method for detecting candidate positions for microcalcifications from a digital mammogram.

  A method for detecting a candidate position of a tumor shadow is described in the following paper. Yin F. F. et al: Computerized detection of masses in digital mammograms: Analysis of bilateral subtraction images, Medical Physics 18,955-963 (1991) Next, a medical image storage communication system (PACS) will be described.

  With the progress of digitalization of images, recently, it has become possible to perform this image diagnosis work using a medical image storage communication system (PACS: Picture Archiving and Communication System). The PACS is a system for supporting a doctor to view medical images by storing, communicating, and displaying medical images (X-ray images, CT images, MR images, etc.) generated in a hospital. The PACS stores the image data sent from the image acquisition device in a database, and transfers the image data from the database to the image workstation when the image is required. The image workstation transmits the image to a cathode ray tube (CRT). Cathode Ray Tube). The doctor makes a diagnosis by looking at the displayed image. An interpretation report that records the diagnosis result can also be created and stored on the PACS. According to PACS, it is no longer necessary to search for the film, carry the film, and put the film on and off the Schaukasten.

  As for the system configuration and functions of the PACS, many technologies have been disclosed. (1) JP 62-121576 A, (2) JP 63-010269 A, (3) JP 64-64 A No. 013837, (4) Japanese Patent Application Laid-Open No. 64-015154, (5) Japanese Patent Application Laid-Open No. 02-103668, (6) Japanese Patent Application Laid-Open No. 02-11840, and the like.

  FIG. 81 is a block diagram showing a schematic configuration of a conventional PACS system.

  PACS has network, IA, WS, and DB components.

  The network performs data communication between components. The IA collects images from various diagnostic imaging equipment. WS displays an image. The DB stores images.

  Next, an outline of the interpretation operation in WS will be described.

  First, an image of a patient is read on the WS in the order of examination numbers. Here, the order of inspection numbers is the newest order of inspection dates. First, the WS sends an unread image transfer request to the DB via the network. The DB retrieves the requested unread image and sends it to the WS via the network. The WS creates an image list according to the order of inspection numbers from the inspection history. Next, the WS sends a transfer request for past images to the DB via the network. The DB retrieves the requested past image and sends it to the WS via the network. Then, the WS first displays the sent unread image and further displays the sent reference (past) image.

  Management of mammogram images taken by mammography using such a medical image archiving communication system (PACS) has led to efficient image diagnosis such as interpretation.

  By the way, when mammography is used as a modality and a mammogram image is diagnosed, there are the following problems at the time of diagnosis.

(1) Many mammogram images of women with a large mammary gland have low optical density in the mammary gland region, and it is difficult to distinguish among them the microcalcification shadow and the tumor shadow.

(2) When comparatively interpreting mammograms, the density of each image was different. An accurate comparative diagnosis could not be made if the image density was different when comparing the corresponding sites.

(3) The enlargement instruction on the image and the specification of the highlighted part are troublesome because the user (doctor) manually inputs using a mouse or the like.

(4) When diagnosing by simultaneously viewing a plurality of images, it is troublesome to arrange the images.

(5) In the detection of the abnormal position by the computer, when the result of the abnormal position is superimposed on the original image and output on the screen, the original image cannot be seen and the diagnostic accuracy is lowered.

(6) The abnormality detection unit may not be applicable to the target image, and if an abnormal result is forcibly given to an image that cannot be applied, the result becomes unreliable.

(7) By just looking at the newest image (current image), even if it appears that there is no abnormality, the change can be found by comparison with the past image. It was troublesome to prepare a comparative image, which caused the performance of diagnosis to be reduced.

  As described above, in the conventional example of mammogram image diagnosis, the burden on the doctor performing interpretation at the time of diagnosis is large, or the doctor cannot obtain information suitable for diagnosis from the image, and the diagnostic ability is reduced. There was a problem.

  Accordingly, an object of the present invention is to provide the following mammography apparatus.

(1) Even in a mammogram image with a dense mammary gland, it is possible to easily distinguish a microcalcification shadow or a tumor shadow.
(2) When comparatively interpreting mammogram images, it is possible to observe with the same density range of the comparison target images.
(3) It is possible to automatically specify an enlargement instruction on the mammogram image and designation of an emphasized part.

  In order to achieve the above object, the present invention takes the following measures.
  The viewpoint of the present invention is that input means for inputting a mammogram image, setting means for setting a closed curve based on a breast contour and a region of interest of a predetermined shape on the mammogram image input by the input means, and the region of interest according to the closed curve A plurality of different moving positions, and predetermined image processing is performed on the image data corresponding to the region of interest at each of the plurality of different positions, and the region of interest at each of the plurality of different positions is handled. A mammography apparatus comprising: image processing means for generating a plurality of display images to be displayed; and display means for displaying the plurality of display images.

  According to the present invention, a mammography apparatus that can achieve the above-described object can be realized.

  Embodiments of a mammography apparatus according to the present invention will be described below with reference to the first to fourth embodiments with reference to the drawings. In the first embodiment, a system that uses digital mammography as a single modality and collectively performs shooting to image output (referred to as a basic system in this embodiment) will be described. In the second embodiment, a system in which a network function is applied to a basic system (referred to as a modality system) will be described. In the third embodiment, a system in which PACS is applied to a basic system (referred to as a PACS system) will be described. In the fourth embodiment, other system variations will be described.

  (First Embodiment) FIG. 2 is a perspective view showing the appearance of the basic system 1. FIG. In the basic system 1, digital mammography is used as a single modality, and everything from shooting to image output is performed collectively.

  The C-arm 5 is formed by integrating the X-ray generation device 2, the compression plate 3, and the X-ray detection device 4, and can be rotated in the direction of the arrow 1a, that is, left and right. Further, the compression plate 3 is movable in the direction of the arrow 1b, that is, the vertical direction.

  FIG. 1 is a block diagram showing a schematic configuration of the basic system 1. The basic system 1 includes an X-ray generator 2, an X-ray detector 4, an input device 6, a RISI / F (interface) unit 8, an output device 10, a system disk 12, a memory 14, a central controller 16, a bar code reader. The system is composed of only one photographing device as in the existing mammography. In addition, since everything from image capturing to output is performed collectively in the system, the basic system itself can be regarded as one modality.

  First, the X-ray generator 2 will be described. The X-ray generator 2 is controlled by the central controller 16. FIG. 3 is a block diagram schematically showing the internal configuration of the X-ray generator 2. The X-ray generator 2 includes an X-ray tube 20, a high-pressure generator 22, an X-ray controller 24, an AEC 30, a filter switching unit 26, a compression pressure controller 28, a photo sensor 32, and a control panel 34. A. A function for setting imaging conditions most suitable for each examination; b. A function of controlling breast compression in relation to X-ray exposure. Each of these two functions a and b will be described.

Regarding the function a for setting the imaging condition most suitable for each examination, the imaging condition setting here refers to the type of filter that defines the quality of X-ray, kVp (X-ray tube voltage), mA (X-ray) The tube current) is set appropriately. The imaging conditions are determined by the imaging condition determination table, which divides the types according to the unique information that varies from patient to patient, that is, the patient's age, breast hardness, breast thickness, and breast size, and gives the imaging conditions for each type. Decide based on. Table 1 shows an example of the photographing condition determination table. Table 1 shows shooting conditions for type A and type B, and is omitted for other types.

  The age of the patient is obtained from examination request information input by the input device 6 described later. Regarding the hardness of the breast, first, the position x where the compression plate 3 touches the breast by moving the compression plate 3 with reference to the position of the detector 42 of the X-ray detection device 4, and the compression plate after a predetermined amount of compression. 3 is measured. The detector 42 will be described later. x is equal to the thickness of the breast when not compressed. Here, the ratio between the compression distance d and the thickness x of the breast when not compressed is defined as an A value (A value = d / x). Then, the hardness of the breast is determined based on the characteristics shown in FIG. That is, the hardness is obtained by giving an A value to a known characteristic curve that gives the hardness of the breast. At this time, the hardness of the breast is roughly divided into three levels: “soft”, “medium”, and “hard”. The size of the breast is obtained by optical measurement by the mechanism shown in FIGS. 5 (a) and 5 (b). FIG. 5A is a side view of the state of measuring the size of the breast by the optical detector 38 and the reflecting plate 40, and FIG. 5B is a view of this state viewed from above. is there.

  Of the light rays 39 emitted from the optical detector 38, the detector 38 detects the light rays reflected by the reflecting plate 40, whereby the reflected light quantity is measured. Then, the size of the breast is obtained from the characteristics shown in FIG. That is, the size of the breast is determined by giving the measured light quantity to a known characteristic curve. The size of the breast may be obtained as follows without depending on the method of optically obtaining in this way. That is, the irradiation field size may be input from the operation panel 34, and the irradiation field size may be used as the breast size. Then, the size of the breast can be obtained simply. FIG. 6 is a diagram showing the operation panel 34, and “12 ″ × 10 ″” and “10 ″ × 8 ″” can be selected as the irradiation field size. The irradiation field size is not limited to these values.

  As for the thickness of the breast, the compression thickness is calculated from the position of the compression plate 3 during compression and the position of the detector 42, and this is used as the breast thickness.

  By the way, regarding the determination of each parameter of the photographing condition, predetermined rules obtained theoretically and empirically are obtained. That is, with respect to the type of filter that defines the quality of X-rays, it is preferable to use a Mo (molybdenum) filter for a normal breast and an Rh (logical) filter for a breast having a large mammary gland region. The filter is switched by the filter switching unit 26 under the control of the AEC 30 described later. As for kVp (X-ray tube voltage), a normal tube is given a low tube voltage of 30 kVp or less, and an image with good contrast can be taken with X-rays in a low dose energy region. Further, a tube voltage larger than 30 kVp is applied to a breast having a large mammary gland region, and radiography with a high dose energy region is suitable for diagnosis. Regarding mA (X-ray tube current), in order to obtain mAs for three large breasts, it is preferable to set the tube current to a large current as well as the energization time. Table 1 is formed based on such rules. The photographing conditions set according to the photographing condition determination table are input to the AEC 30 as thickness / size / hardness data 36.

  Here, the AEC 30 will be described. An AEC (Automatic Exposure Control) 30 obtains a control amount for exposing X-rays with an appropriate dose. The obtained control amounts are used as an X-ray controller 24, a filter switching unit 26, and a compression pressure control unit 28. To control exposure. At this time, there are two methods for obtaining a desired control amount. One of them is to destructively read out data of a specific pixel from the detector 42 at regular intervals during exposure, and it is appropriate for the pixel having the lowest optical density among those data (AEC data). This is a technique for obtaining an X-ray exposure dose for giving a dose. The exposure time is controlled by the obtained exposure dose. This technique is applied when the detector is a flat detector. FIG. 7 shows a data collection point 44 for reading a specific pixel in the detector 42. The other is, as shown in FIG. 8, an AEC detector 46 comprising an intensifying screen and a photodiode is provided below the data collection point 44 of the detector 42, thereby enabling destructive readout of the detector data. It is a prescription that collects AEC data without doing it. An X-ray exposure dose for giving an appropriate dose to the pixel having the lowest optical density among the outputs of the AEC detector 46 is obtained. The exposure time is controlled by this exposure amount.

  Next, the function b that controls breast compression in relation to X-ray exposure will be described. Pressing the breast with equal pressure from setting to the end of imaging may put a burden on the patient. For this reason, in order to relieve the compression of the breast as much as possible, the compression is appropriately controlled. In other words, the pressure is slightly loose before shooting, plus compression is performed immediately before shooting, an appropriate compression value is set, and the image is released immediately after the end. In this way, the patient's pain can be eased.

  First, a mechanism for compressing the breast will be described. FIG. 9 is a cross-sectional view of the mechanism portion that compresses the breast with the compression plate 3 as seen from the side. The compression portion 48 is configured by integrating the compression plate 3, the compression plate support portion 49, and the pressure sensor 50. The compression unit 48 can move freely in the vertical direction, and is driven by applying pressure to the upper surface of the pressure sensor 50. As shown in FIG. 10, the compression part 48 is driven by pressurizing the oil 51 as shown in FIG. 10. When pressing the breast with the compression plate 3, the lower hydraulic pressure is released while the breast is sandwiched. Pressurize the oil pressure while controlling the pressure with the pressure sensor 50. When releasing the breast from compression, the upper hydraulic pressure is released and the lower hydraulic pressure is increased to raise the holding plate. FIG. 11 is a block diagram showing a schematic configuration of such a breast compression mechanism. The control unit 52 controls the movable unit 54 based on a signal from the pressure sensor 50 and a preset set value 56 to drive the compression plate 3. Here, the breast compression mechanism does not depend only on the mechanism as shown in FIG. For example, the compression plate 3 itself may have a function of controlling pressure.

  Next, two methods for appropriately controlling the timing of compression so as not to burden the patient will be described. By these methods, the compression pressure control unit 28 controls the breast compression mechanism described above according to an instruction from the AEC 30. FIG. 12 is a diagram for explaining the first technique, and shows a process of compressing the breast in relation to X-ray exposure. Here, FIG. 12A is an X-ray generation signal timing diagram, FIG. 12B is an x-ray (X-ray) exposure timing diagram, and FIG. 12C is a pressure timing for pressing the compression plate 3. FIG. In addition, the pressure shown in FIG.12 (c) is represented by the percentage (%) when the pressure required at the time of X-ray exposure is set to 100%.

  First, an X-ray engineer in charge of imaging gives a compression instruction to the control unit 50 by using a console (not shown) or the like, and compresses the breast with a pressure actually required at the time of X-ray exposure. The pressure value at that time is read by the pressure sensor 50 and stored as an appropriate pressure value in a memory (not shown) of the control unit 52 (setting period). Next, the control unit 52 waits for 80% of the stored pressure value (standby period). Then, using the X-ray generation signal (a) as a trigger, the pressure is increased to 100%, that is, an appropriate pressure value, and then x-ray (b) is generated to perform imaging (during X-ray generation). Immediately after shooting, the pressure shall be completely released. Note that the compression rate (80% here) during the standby period can be changed as appropriate.

  FIG. 13 is a diagram for explaining the second technique. 13A is an X-ray generation signal timing diagram, FIG. 13B is an x-ray (X-ray) exposure timing diagram, and FIG. 12C is a pressure timing diagram for pressing the compression plate 3. is there. In addition, the pressure shown in FIG.13 (c) is represented by the pressure value. First, at the time of setting, an X-ray engineer gives a compression instruction to the control unit 50 by using a console (not shown) or the like, and presses the breast appropriately (slightly loosely) and waits (setting and waiting period). Then, using the X-ray generation signal (a) as a trigger, pressurization is performed up to a preset set pressure value, and then x-ray (b) is generated to perform imaging (during X-ray generation). Immediately after shooting, the pressure shall be completely released. The set pressure value can be changed as appropriate. Next, the X-ray detection apparatus 4 will be described. The X-ray detector 4 is controlled by the central controller 16. FIG. 14 is a block diagram schematically showing the internal configuration of the X-ray detection apparatus 4. The X-ray detection device 4 includes a readout time setting device 60, a timing generation device 62, a driving device 64, a detector 42, a readout device 68, an A / D conversion unit 70, and a readout range setting device 72. It has device control and data read functions. In this embodiment, the X-ray detection device (detector 42) is a TFT flat detector. FIG. 15 is a circuit diagram showing a configuration of a TFT flat detector (hereinafter simply referred to as detector 42). The array 73 is composed of a plurality of cells arranged in a two-dimensional lattice state. One cell includes a FET (a-Si: H) 80 connected to the gate line 76 from the driving device 64 and a data line 78 from the reading device 68, and a sensor (a-Si: H) connected to the FET 80. ) 82 and a capacitor (not shown). The sensor 82 is a photodiode that detects photon photons. An intensifying screen (not shown) is placed on the array 73 and converts the X-rays exposed to the array 73 into light. Instead of the intensifying screen, a material coated with a material having a scintillation function for converting X-rays into light may be used.

  The drive device 64 creates a control pulse for detecting a signal based on the read range set by the read range setting device 72 and the timing pulse corresponding to the read time set by the read time setting device 60. Then, the detector 42 is driven.

  Here, device control and data reading for X-ray detection in the X-ray detection apparatus 4 will be described. First, the detector 42 performs an initial setting for discharging the electric charge accumulated in the capacitor of each cell of the array 73. Next, X-rays are exposed to the subject by the X-ray generator 2. X-rays that have passed through the subject reach the intensifying screen placed on the detector 42. The X-rays that have reached the intensifying screen are converted into light here. The photodiodes (sensors 82), one for each cell on the array 73, detect the light (photon photons) converted by the intensifying screen and convert it into an electrical signal. The obtained electric signal is temporarily stored in the capacitor as electric charge.

  When the X-ray exposure ends, that is, when the high voltage generation signal of the X-ray controller 24 changes from ON to OFF, the control pulse generated in the driving device 64 described above is supplied to the array 73 as a trigger, and the array 73 73 TFT element (FET80) is turned on. Then, the reading device 68 reads the electric charge stored in the capacitor as an analog signal via the data line 78. Here, the reading device 68 performs control such as integration by an operational amplifier and parallel reading. The analog signal read out in this way is A / D converted by the A / D conversion unit 70 and converted into a 14-bit digital signal (may be 16 bits or the like) for each pixel. In this embodiment, a digital signal having a predetermined bit width is defined as a pixel value. Image data constituted by a matrix of a plurality of pixel values is transferred to the memory 14.

  The readout device 68 can change the image readout time according to the drive timing generated by the timing generator 62. The drive timing is changed by the read time setting device 60. In addition, when the image is read out in the small irradiation field at the time of the size of the breast and biopsy, the reading range can be limited with the intention of efficient image reading. The biopsy will be described later.

  The reading range is limited by limiting the control line, that is, the gate line 76 to which the control pulse is transmitted by the reading range setting device 72, and limiting the signal line to be read, that is, the data line 78.

  As a post-process for imaging, after the above-described image acquisition is completed, when X-rays are not exposed (when the high-voltage generation signal of the X-ray controller 24 is OFF), the image is darkened by the capacitor of the array 73 again for the same time. Accumulate the time signal. A control pulse for turning on the FET 80 is sent to the detector 24 to collect image data and store the dark result in the memory 14. The dark image data is subtracted from the finally collected X-ray image data, and this is stored in the memory 14 as a collected image.

  By the way, although the present Example demonstrated the case where a TFT plane detector was used as an X-ray detection device, it is not limited to this. For example, if a screen-film system is applied and the photographed film is digitized by a digitizer, detection data can be obtained in the same manner as a TFT flat panel detector. In this case, real-time imaging control based on the detection data is impossible. An imaging plate may be used as the X-ray detection device. In this case as well, shooting control is impossible. In addition, the slot scan method may be applied as an X-ray detection device. In this case, the imaging time cannot be set during imaging, so pre-exposure is performed first, and imaging conditions including the imaging time are set. It is preferable to keep it. A two-dimensional CCD may be used as an X-ray detection device. In this case, real-time imaging control based on the detector data is possible, and data in the same format as the TFT flat detector can be obtained as image data (detection data) and stored in the memory.

  Next, the input device 6 will be described. The input device 6 has five functions. That is, a. A function for inputting patient information and examination information; b. A function for inputting control of the output screen; c. A function of inputting an interpretation doctor ID; d. Function for selecting interpretation and inspection mode, e. A function of selecting an output means; The input device 6 will be described for these functions a to e. FIG. 16 is a diagram illustrating screen transition of the operation panel 90. The operation panel is configured by a touch screen.

  First, the function a will be described. Function a is for inputting patient information and examination information. A description will be given of the case where the system is connected to the RIS and the case where the system is not connected to the RIS. The RIS is a system for obtaining information from an external system, and will be described in detail later.

First, when there is no information input from RIS, patient information and examination information are inputted from examination request information. In this case, since the inspection request information is a paper surface, the operator inputs it from a keyboard or the like (not shown). The patient information is a patient name, patient ID, and the like, and the examination information is examination ID, part, direction, and the like. Table 2 shows an example of inspection request information. In Table 2, the examination request information about the patient ID-880841 and the patient name-Yamayama child is described.

  Next, a case where information is input from the RIS will be described. When information can be input from the RIS, the digitized inspection request information is sent from the RIS via the RISI / F unit 8 and stored in the memory 14. Individual examinations are registered in the order of arrival in the memory 14.

  The individual examinations registered as described above are displayed on the operation panel. However, when the operation panel 90 is configured by a touch panel, a target examination can be selected via the touch sensor. FIG. 17 is a view showing an examination (patient) list panel displayed on the operation panel, and shows a state where the selected examination, that is, the display line of the selected patient name is highlighted.

  Next, the function b for inputting output screen control will be described. First, a case where the operation panel 90 is configured by a touch panel will be described. FIG. 18 is a diagram illustrating an operation panel that performs input for output screen control. Here, (a) in the figure shows an image selection panel, and (b) in the figure shows a selection panel for a detailed display ROI. In the image selection panel of FIG. 18A, two types of schemas 92 that abstract an image are displayed on the operation panel 90, and characters (for example, “CC image”) indicating the part and direction of the image are displayed. , “ML image”). When one of these schemas 92 is touched with a finger or the like, the schema 92 that is touched with a finger (not shown) is highlighted and an image can be selected. Further, on the selection panel of the detailed display ROI in FIG. 18B, the schema 92 is displayed with a grid. When it is desired to observe the details of the image, the details of the image are displayed on the CRT when the portion of the displayed grid that is to be observed is touched.

  Here, the schema 92 may be such that only the edge (breast contour) is drawn by detecting the skin edge of the subject (breast) in the actual image using a sobel operator operator.

  Next, the case where the operation panel 90 is comprised by means other than a touch panel is demonstrated. FIG. 19 is a perspective view of the image selection panel. The image selection panel 94 is constituted by a mechanical switch 95, and an image is selected by pressing this switch. FIG. 20 is a perspective view of a detail display ROI selection panel. The detail display ROI selection panel 96 is constituted by a mechanical switch 95 as in the case of the image selection panel 94, and selects a portion for which details are to be observed by pressing this switch. Each position of the mechanical switch 95 corresponds to the position of the irradiation field of the displayed image.

  Next, the function c for inputting the interpretation doctor ID will be described. When the operation panel 90 is configured by a touch panel, an interpretation doctor ID input panel is displayed as shown in FIG. The doctor who interprets the image inputs the ID through the ID input panel 98. Next, the function d for selecting the inspection and interpretation mode will be described. As shown in FIGS. 16A to 16C, the mode is selected on the display of each panel. After selecting the mode, the function in each scene can be executed.

  Next, the function e for selecting the output means will be described. As shown in FIG. 16D, an image is output to a film (“4.1 CRT output”), an image is output to a film (“4.2 film output”), and an image is output to a film and a CRT (“4.3 The output form such as “Film & CRT output”) can be selected.

  According to the functions a to e described above, it is possible to deal with a screen and an interpretation style according to the interpretation doctor's preference.

  Next, a case where the present system (basic system) obtains data from another system by using an external system / connection interface will be described in detail. Here, a case where data is obtained from the RIS (Radiology Information System) via the RISI / F unit 8 will be described.

  First, for data transfer functions and routines from other systems, as described above, digitized inspection request information is sent from an external RIS and converted into a data format that can be processed as information by this system. And then stored in the memory 14. Further, individual examinations are registered in the examination list in the order of arrival in the memory 14. When displayed on the touch panel, the target examination (patient) can be selected via the touch sensor as shown in FIG.

Next, as an example of the data structure of the RIS data, the configuration of the inspection request information is the same as that shown in Table 2 above. Further, Table 3 shows the structure of an interpretation report as a result of the inspection.

  Next, the output device 10 will be described. FIG. 22 is a block diagram showing the internal configuration of the output device 10. The output device 10 inputs the processed image data and character / symbol data (hereinafter referred to as information) composed of character data and screen (symbol) data from the memory 14 and outputs the data to the screen or film 102 of the CRT 100. An image reduction / enlargement processing unit 104, a screen creation unit 106, a frame memory 108, an overlay memory 110, a display management unit 112, a D / A conversion unit 114, a barcode generation unit 116, and a laser writing device 118.

The frame memory 108, the overlay memory 110, the display management unit 112, and the D / A conversion unit 114 are dedicated devices for outputting images and information on the screen of the CRT 100. The bar code generation unit 116 and the laser writing device 118 are This is a dedicated device for outputting images and information to the film 102.

  When outputting an image and information on the screen of the CRT 100, that is, when selecting “CRT output” by the operation panel 90 of the input device 6 described above and giving an instruction to the display management unit 112 for output, The reduction processing unit 104 performs image processing such as reducing or enlarging the image data sent from the memory 14 to a predetermined size, and sends the image data to the screen creation unit 106. The screen creation unit 106 creates a screen by arranging the processed image data at a predetermined position, and writes the screen in the frame memory 108. The character / symbol data is written to the overlay memory 110. Then, the display management unit 112 superimposes an overlay with a predetermined number instructed by the central controller 16 on the frame memory 108 and sends it to the D / A conversion unit 114. The D / A converter 114 converts the contents of the frame memory 108, which is a digital signal, into an analog signal (D / A conversion) and outputs it to the screen of the CRT 100.

  When outputting an image and information to the film 102, that is, when selecting “film output” by the operation panel 90 of the input device 6 and giving an instruction to the laser writing device 118 for output, the image is reduced or enlarged. The processing unit 104 performs image processing such as reducing or enlarging the image data sent from the memory 14 to a predetermined size, and sends the image data to the screen creation unit 106. In addition, the barcode generation unit 116 generates a barcode based on predetermined information sent from the memory 14 and sends the barcode to the screen creation unit 106. The predetermined information for generating the barcode is information unique to the inspection such as the inspection ID and the image number recorded in the inspection request information. The screen creation unit 106 arranges the sent image data at a predetermined position, creates output data by superimposing the image data, character / symbol data (binarized data), and a barcode, and creates a laser writing device 118. Send to. The laser writing device 118 outputs output data to the film according to an instruction from the central processing unit 16. FIG. 23 is a diagram illustrating an example of the output film 102. A bar code 120 is written on the film 102 at a predetermined position.

  Next, the system disk 12 will be described. The system disk 12 stores a control program for realizing the following functions. However, the following functions may be implemented in hardware for the purpose of speeding up.

a. Means for recognizing the mammary gland region and enhancing contrast b. Means for adjusting the density range c. ROI position determining means, shuttle handling means d. Image processing means e. Abnormal shadow detection means applicable discrimination means f. Abnormal shadow detection means, detection result storage means g. Output screen creation means h. Anomaly detection result output means i. Means for recognizing the shooting direction from the tilt of the arm j. Compression timing adjusting means k. Biopsy puncture status confirmation means l. Biopsy visual field recognition and partial data storage means m. Automatic setting means for photographing conditions by a photographing scene and a detector (mode) n. Means for reading out an image triggered by the end of exposure o. Patient information input / output means from RIS, identifier output means p. Means for scaling the image to an arbitrary size q. CRT, film output selection means r. Means for discriminating abnormal malignancy and benign and outputting the result s. ROI manual input means t. Overall control program First, when the system is started up, the central control unit (CPU) 16 starts up the overall control program (described later), and from the input device or the like according to each use scene (described later). Execute each function triggered by an event.

  Next, each function of a to t will be described.

  a. Means for Recognizing Breast Gland Region and Enhancing Contrast When taking a pixel histogram of an image, the normal breast (breast) histogram has a shape as shown in FIG. 24, and the breast region has a dense breast (dense breast). The histogram is as shown in FIG. Here, in FIG. 25, the anatomical structure to be diagnosed cannot be seen unless the contrast of the region A having a high pixel value is high. Therefore, in order to recognize the anatomical position of the region A, first, an n pixel × n pixel minute region (hereinafter referred to as ROI) 122 as shown in FIG. Among them, a bright ROI (ROI having a high pixel value) is selected. Next, a representative value (for example, median value, median value) of the pixel of the selected ROI 122 is displayed, and a lookup table for converting the pixel value into luminance so as to obtain the highest luminance (brightness) of the output is displayed. Change to enhance contrast. FIG. 27 is a diagram illustrating a relationship between a pixel value and a gray scale (luminance). The slope of the straight line 128 representing the correspondence relationship between the pixel value after contrast enhancement and the gray scale (luminance) is compared with the straight line 126 representing the correspondence relationship at the time of output from the detector, that is, the straight line before the lookup table is changed. The contrast is enhanced by changing the look-up table so that it becomes large. Here, the contrast enhancement may be performed by changing the pixel value of the image data so that the slope of the straight line 128 is larger than the slope of the straight line 126, not only when the lookup table is changed.

  In contrast enhancement, if the slope of the straight line 128 becomes too large, noise may be enhanced. For this reason, it is preferable to limit the noise enhancement level.

  b. Means for Adjusting Density Range (Aligning Image Density) FIG. 28 is a diagram schematically showing the flow until the left and right breast images are displayed or output. The captured image initially exists in the image memory bank 129 composed of an IC memory, a magnetic disk, or the like. When an instruction to display an image of a specific patient taken from a specific direction is issued, the left and right breast images are first sent to the density equalization processing unit 130 to create a composite image 132. The composite image 132 is an image in which two images of the left and right breasts are arranged in order to display or output the left and right breasts as one image, and an image in which the average image density of the left and right images is uniform. Point to. The created composite image 132 is sent to the frame memory 108, the overlay memory 110, and the laser writing device 118, and then displayed on the CRT 100 or output to the film 102. Note that the operation of the output device 10 when the composite image 132 is output is the same as that described above, and is therefore omitted.

  Here, the density equalization processing unit will be described in detail. FIG. 29 is a diagram showing a specific example of processing of the density equalization processing unit 130, and shows an example of processing for making the average density in the ROI 133 of the left and right breast images the same. In the present embodiment, a case where processing is performed so that the average density of the right image is aligned with the average density of the left image will be described, but this may be the same as the average density of either the left or right image. A third average density different from the average density of the image may be used.

First, the average value calculation unit 134 calculates average values m ₁ and m ₂ of the pixel values of the left image and the right image, respectively, and then calculates a ratio of m ₁ and m ₂ by the division unit 135. Then, the image calculation unit 136 calculates the average density of the right image based on the obtained ratio value so that the average density in the ROI 133 is the same as the average density of the left image, and the left and right image densities are the same. A composite image 132 is created.

  Although the ROI 133 is normally set in advance, it is desirable that not only the fixed ROI such as the ROI 133 but also a special ROI (free ROI) given by the operator can be received and processed. . In addition, the ROI 133 can be set in a region centered on a portion pointed out by the CAD as a lesion candidate.

  As another example of density equalization processing, in addition to the example in which the average values of pixels are aligned as described above, an example in which the median value, mode value, and histogram in the ROI are aligned is also known.

  Moreover, it is good also as a process which arrange | equalizes the standard value of a pixel while aligning the average value of a pixel.

c. ROI position determining means, shuttle handling means, for example, the position of the ROI for performing enlarged display as image processing can be automatically set and moved.

  FIG. 30 is a diagram showing the ROI for enlarged display and the locus of position movement of the ROI center. The ROI 133 is composed of 4A pixels × 5A pixels (A is a natural number) of the image. Here, XY coordinates are set, and the contour 137 obtained by moving the contour 138 of the extracted subject (breast) 3A toward the inside of the breast in the X direction, a straight line X = 4000-2A, and a straight line Y = 3A A first closed curve 139 surrounded by a straight line Y = 5000-3A is formed.

  Next, the image data in the ROI 133 is enlarged while moving the center of the ROI 133 on the first closed curve 139 and displayed on the CRT 100 of the output device 10. When the ROI 133 completes the first closed curve 139 once, the position movement is temporarily stopped.

  Next, an outline obtained by moving the breast outline 138 further in the X direction by 3A × 2, and a straight line X = 4000-2A × 2, a straight line Y = 3A × 2, and a straight line Y = 5000-3A × 2 Create an enclosed second closed curve 140. Similarly to the case of the first closed curve 139, the image data in the ROI 133 is enlarged while moving the center of the ROI 133 on the second closed curve 140 once and output to the CRT 100 of the output device 10. In FIG. 30, the second closed curve 140 is not shown.

  The above processing is repeated until the X coordinate value of the leftmost point of the contour line becomes smaller than 4000-2A × N (N is a natural number). Further, the movement from the closed curve N to N + 1 is performed linearly. FIG. 31 shows a trajectory when the position movement of the ROI center is continuously performed.

  Note that the contour line 137 to be extracted first may be obtained by approximating the breast contour 138 with a polygon as shown in FIGS. 32A and 32B by way of example. Further, the size of the ROI 133 to be displayed (determination of the value of A) is determined by the enlargement ratio. This enlargement ratio is set in advance by the inspector before the inspection. FIG. 33 shows an example in which enlarged display is performed with the ROI 133 set in this way.

  The ROI position determination for image processing has been described for the case of performing enlarged display as image processing. However, the case of performing other image processing, such as contrast enhancement, is the same as that for enlarged display. FIG. 34 shows an example where contrast enhancement is performed. Means for performing various image processing will be described later. In addition, as a method for extracting the breast contour 138 and a method for setting the contour line 137, a known method such as automatic extraction may be used. It can also be set by the inspector using a shuttle.

  Observation can be performed by automatically moving the ROI according to the shape of the breast appearing in the mammogram image. FIG. 35 shows the locus of ROI position movement corresponding to various mammogram images.

  d. Image processing means The image processing means can perform the following three types of image processing.

1. Image processing that enhances an appropriate frequency region such as unsharp masking and makes it easy to see shadows and the like is performed. For unsharp masking, you can refer to the following paper: Leh-Nien D.loo, "Investigation of basic imagingpropertiesindigital radiography 4.Effect of unsharp masking on detectability of sample patterns", Med. Phys. 12 (2), pp. 209-214.
2. As described in the contrast enhancement means, image processing for enhancing the contrast by changing the lookup table is performed.

3.2. The image processing for converting the density range into a certain range is performed in the process before all image processing is performed. As shown in FIG. 36, when the pixel range is A (over exposure) or B (under exposure), the pixel range is converted to a C pixel range (appropriate exposure).

  e. Means for determining whether or not an abnormal shadow detection means is applicable In the mass shadow detection method, an abnormal shadow is detected by obtaining a difference between pixel values of left and right breasts. However, this method cannot be applied when the size and shape of the left and right breasts are extremely different. Therefore, in the present embodiment, the following two processes are performed to determine whether the tumor shadow detection method is applicable. If it is determined that application is not possible, the output device 10 outputs a comment to that effect without applying the abnormal shadow detection means.

1. Check the left and right areas of the breast.

  As shown in FIG. 37, the image is divided into two regions, region A and region B, and the area of region B is defined as the breast area. Regarding the division of the region, the p point (pixel value p) may be used as a threshold (a threshold value) for division in the breast image histogram shown in FIG.

  The areas obtained for the left and right breasts are compared, and if the difference is, for example, 10% or less of the entire area, it is determined that the tumor shadow detection means can be applied.

2. Check the angle of the breast contour.

  As shown in FIG. 38, a circle is superimposed (fitting) on the breast contour, and an angle formed by a straight line connecting the midpoint 142 of the arc included in the image and the center of the circle and the horizontal line of the image is defined as a contour angle 144. The contour angles obtained for the left and right breasts are compared, and the tumor shadow detection means is applied if the angle difference is, for example, 10% or less of the total angle.

  As for contour detection and the like, a technique of binarizing and extracting using a Sobel operator or the like is known.

f. Abnormal shadow detection means, detection result storage means As means for detecting abnormal shadows and the like, microcalcification shadows and tumor shadows are detected by the above-mentioned CAD (computer-aided diagnosis). These means for detecting abnormal shadows are sequentially applied to the mammogram image, and the detection results are described in the abnormality detection result table and stored in the system disk 12 as, for example, a data file. When the detection results are sequentially output, they are stored in the memory 14 and output. Table 4 shows an abnormality detection result table.

  g. Output screen creation means <Mamogram image placement method management means> As the function 1, the output screen creation means can determine the placement method of images on the screen according to the preference of the doctor. Further, as the function 2, the arrangement method can be determined according to the abnormality detection result from the image.

  FIG. 39 is a diagram showing types of shooting directions. For example, FIG. 4A shows a case where X-rays are taken for the right breast in the vertical direction, particularly “from top to bottom” (from the head of the subject to the legs) and imaged by exposing the X-rays. Yes. During imaging, the breast is pressed and pinched perpendicular to the direction of X-ray exposure.

  In FIG. 39, six types of patterns (a) to (f) are shown for the right breast as the imaging direction, but in this embodiment, the imaging directions are two types, the vertical direction and the horizontal direction. There are two types of mammogram images for each direction. That is, for the up and down direction, the “top to bottom” direction and the “bottom to top” direction are not distinguished, and for the left and right direction, the “inside to outside” direction and the “outside to inside” direction are not distinguished. In addition, this is not taken into consideration for the oblique direction (photographing is not performed).

  The arrangement method on the screen is set according to the type of mammogram image for each photographing direction. In this embodiment, two CRTs are provided and different images can be displayed on each CRT. In each CRT, two images are simultaneously displayed on one screen.

  FIG. 40 is a diagram showing types of image placement methods on the screen. FIG. 40A is a diagram showing types of placement positions, and FIG. 40B is a diagram showing types of placement directions.

  As shown in FIG. 5A, the screen layout position includes a left layout position L and a right layout position R when the screen is divided vertically, and an upper position when the screen is divided horizontally. There is an arrangement position U and a lower arrangement position D.

As shown in FIG. 4B, there are four types of arrangement directions (1) to (4) as the arrangement directions on the screen. For each type of image (represented by cases 1, 2, and 3), the doctor holds a favorite arrangement method according to the abnormality detection result as a table in the memory 14 or the system disk 12. Table 5 shows the contents of the table held by the three doctors A, B, and C.

  FIG. 41 is a diagram illustrating a state in which images are arranged on the screens of two CRTs on the left side and the right side for each type of image (for each case) based on the table in Table 5 held by the doctor A.

  FIG. 42 is a diagram illustrating a state in which images are arranged on the screens of two CRTs on the left side and the right side for each type of image (for each case) based on the table in Table 5 held by the doctor B.

  FIG. 43 is a diagram showing a state in which images are arranged on the screens of two left and right CRTs for each type of image (for each case) based on the table in Table 5 held by the doctor C. The doctor C always outputs in a constant arrangement method regardless of the abnormality detection result.

  Next, an operation until output on the screen according to the determined arrangement method will be described.

1) The doctor inputs doctor identification information (doctor ID number) before interpretation.

2) If the inputted doctor ID number is registered in the table, the central controller 16 instructs the arrangement method of the image to be displayed according to the registered contents. Here, if a doctor ID number is not registered in the table, a default arrangement method (a preset arrangement method, for example, an arrangement method similar to that of doctor A) is followed.

3) If the image matrix size to be displayed matches the display area matrix size of the display device, the image is displayed in the designated arrangement position and arrangement direction as it is. If the image matrix size does not match the display area matrix size, the image data is processed into image data and displayed at both ends in order to match the image matrix size with the display area matrix size.

  Regarding the processing of the image data, for example, the image data size is (4000 × 5000), and the matrix size of the display area is (4000 × 5000).

  Here, in the case of displaying at the arrangement positions “L” and “R”, the matrix size of the area required for the display is (2000 × 5000), so that it is indicated by hatching as shown in FIG. Delete the area.

  Further, when displaying at the arrangement positions “U” and “D”, the matrix size of the area required for the display is (4000 × 2500), so that the area is indicated by hatching as shown in FIG. Delete the area.

  As described above, according to the output screen creation means, the arrangement method of the image on the screen can be variously determined according to the doctor's preference or according to the abnormality detection result, and is necessary according to the determined arrangement direction. If so, an output screen can be created by processing image data.

  Note that the shooting direction and the number of images are not limited to those shown in Table 5 above, and a plurality of images such as “left diagonally up to right diagonally down” and “right diagonally upside down to left diagonally down” are displayed in the diagonal direction. You may shoot. Further, the number of display devices is not limited to two. For example, the number may be one, or three or more may be used to display in various arrangement directions.

h. Abnormality detection result output means As the function 1, the abnormality detection result output means can indicate the position of the abnormality detected by the abnormal shadow detection means from the outside of the image. As function 2, the number of detected abnormalities can be indicated. Further, as function 3, an identifier can be attached to a plurality of abnormalities, and each can be clearly identified.

  The abnormality detection result output means satisfies both conflicting requests from an observer (interpretation doctor) who wants to refer to the abnormal shadow detection result but does not want to disturb the image interpretation.

  FIG. 45 is a schematic diagram of a screen in which abnormal shadow detection results are shown from the outside of the image. According to FIG. 45A, a mammogram image 146 showing the detected abnormality (shadow) 148 on the screen 145, two markers 147 located outside the mammogram image 146, and the detected abnormality (shadow) are displayed. Expression 149 is displayed. In FIGS. 45A to 45C, the marker 147 is displayed as an arrow. The marker is not limited to an arrow. The marker 147 is positioned outside the mammogram image 146 so that the intersection point on the extension line of the arrow of each marker is equal to the position of the detected abnormality 148.

  When there are a plurality of detected abnormalities and the number is relatively large, the display becomes troublesome when the abnormalities are indicated by a plurality of markers as described above.

  Therefore, as shown in FIG. 45 (b), while displaying one abnormal position from the outside of the image, the number 149 of abnormalities (shadows) detected to have other abnormalities is displayed in the corner of the screen. As a result, it is understood that there is a detected abnormality in addition to the abnormality indicated by the marker.

  As shown in FIG. 45C, an identifier 152 such as a number may be displayed near the detected abnormal position.

  In addition, as shown in FIG. 45 (d), when it is desired to indicate the positions of a plurality of abnormalities at once using a plurality of markers from the outside of the mammogram image, the shape or color of the markers may be changed and displayed.

  As shown in FIG. 45 (e), the positions of the markers that indicate the position of the abnormality (shadow) from the outside of the image are the X-axis and Y-axis from the coordinates (x, y) of the detected abnormality in the image. It can be obtained by intersection points (x, 0) and (y, 0) of the extended perpendicular lines.

<Comparison of CAD result> As a main function, the diagnosis result of the past image and the diagnosis result of the current image by the above-mentioned CAD (Computer Aided Diagnosis) are compared and displayed when there is a difference between the past image and the current image. .

1) The central control device 16 performs CAD processing (abnormality detection) on the current image to obtain a CAD processing result.

2) The central control device 16 searches for past images from the patient identification information (patient ID).

3) The central control device 16 compares the CAD processing result of the past image (if the CAD processing result does not exist, executes the CAD processing to obtain the result) and the CAD processing result of the current image.

4) If there is a difference between the two results, the central control device 16 outputs that fact.

5) The doctor inputs a comparative interpretation command.

6) The central control device 16 outputs the current image and the past image to the display device 10 according to the table shown in Table 6 below. In Table 6, only the table for the case 1 of the doctor A is shown, and the table of the other case of the doctor A and the table of the other doctor are omitted.

  FIG. 46 is a diagram illustrating a state in which the current image and the previous image (past image) are arranged on the screens of two CRTs based on the table in Table 6, respectively.

  If there is a difference between the two results, the current image and the past image may be displayed without waiting for the doctor's comparative interpretation command input.

  An image obtained by the X-ray detection device 4 is stored in the temporary memory 14 and output from the output device 10. The interpreter makes a diagnosis based on the output.

  At this time, as an auxiliary role of image interpretation, in this system, abnormal shadows are detected, and image processing is automatically performed based on this result so that abnormal shadows are displayed more clearly. . As image processing, enlargement, contrast adjustment, frequency processing, and the like are performed. The image interpreter sets in advance which image processing is performed. When abnormal shadow is performed, the image processing set automatically is performed and displayed.

  As a display method, first, a display screen after image processing and a standard display screen are set. At this time, a plurality of (for example, two) CRTs are used in accordance with the number of screens, a display screen after image processing is set on one CRT, and a standard display screen is set on the other one. Further, the CRT may be configured with only one unit, and a plurality of screens may be realized by dividing the screen.

  The standard screen is displayed as it is when the image information amount and the screen displayable information amount are the same, but when the image information amount is larger than the screen displayable information amount, the image information is compressed and displayed. Means for compression include averaging and thinning.

  Next, the image that has been subjected to image processing is displayed on the image processing screen. At this time, the detected abnormality position is displayed at the center of the screen.

  When enlarging as image processing, the image information may be displayed as it is (when the amount of image information is larger than the amount of image display information) or may be displayed by interpolating information between pixels.

  When adjusting the contrast for image processing, the pixel value range of the displayed image is reduced compared to the standard image when enlarged, and the difference between the maximum and minimum signals is small. Adjust. 47A and 47B are diagrams for explaining the contrast adjustment. FIG. 47A shows the input / output characteristics of the standard image, and FIG. 47B shows the input / output characteristics of the image after the contrast adjustment. (C) is a diagram showing a display example of a standard image, and (d) is a diagram showing a display example of an image after contrast adjustment.

  Abnormal shadows appear on mammogram images due to various factors such as calcification and tumor shape. The abnormal shadow detected by the abnormal shadow detection means is subjected to image processing in accordance with such various factors and then displayed.

  In the image processing means described above, with regard to frequency processing, the frequency characteristics of the image are changed according to various factors. For example, when an abnormal shadow appears on the image due to calcification, such a shadow has a relatively high contrast, but since it is a slight shadow, the contour is further enhanced by enhancing the high frequency range. Make it clear. Further, when a tumor appears on the image as an abnormal shadow, such a shadow is judged (interpreted) based on a slight difference in shading on the image, so that it is easier to see the image if the low frequency range is emphasized. Thus, by changing the frequency characteristics of the image, the abnormal shadow can be displayed more clearly.

  It should be noted that where the range (for example, ROI) of the image displayed on the image processing screen is on the standard image is also displayed on the standard image.

  As shown in FIG. 48A, when there are several abnormal shadows, the screen is divided and displayed according to the number. Since image processing is performed on each of the divided screens, the degree of image processing varies depending on each screen. At this time, a number or the like may be added as shown in FIG. 48B in order to make it easy to understand where the standard screen is displayed. If the number of abnormal shadows is too large to be displayed, the radiographer is informed by sound or a message so that it can be seen that all are not displayed. As for the image processing that is automatically performed, the image reader can set the contents of the image processing in advance, and therefore it is possible to perform image processing other than the above-described image processing.

  By configuring as described above, it is possible to perform interpretation by quick operation, and it is possible to realize excellent lesion detection ability.

  i. Means for Recognizing Shooting Direction from Arm Inclination <Automatic Recognition of Shooting Direction> FIG. 49 is a side view of the C-arm and the C-arm support. In the figure, the X-ray generator 2, the compression plate 3, the X-ray detector 4 and the like provided on the C arm 5 are omitted. The C arm 5 is attached to the C arm support portion 154 so as to be rotatable.

  According to the automatic recognition of the photographing direction, it is possible to automatically obtain a part of the accompanying information such as “inspection information” in Table 3 described above and simplify the input. Here, the photographing method is automatically recognized from the inclination of the C-arm 5. That is, as shown in FIG. 49, the inclination angle θ of the C arm 5 is defined, the inclination angle θ of the C arm 5 is obtained, the contents to be entered in the item of the photographing method of the accompanying information are determined, and written and stored in the memory 14.

  FIG. 50 is a diagram schematically showing processing for automatically recognizing the shooting direction in this way. First, in S1, the rotation angle of the C arm 5 is recognized using a mechanism that automatically recognizes the rotation angle.

  FIG. 51 is a perspective view showing an outline of a mechanism for automatically recognizing a rotation angle. As a method for automatically recognizing the rotation angle, first, the first gear 158 is attached to the rotation shaft 156 of the C arm 5, and the second gear 160 is engaged with the first gear 158. A variable resistor (not shown) is attached to the rotation shaft of the second gear 160 so as to be rotatable in the same manner as the rotation shaft, and the rotation angle is converted into a resistance value by the angle recognition unit 162 to electrically The angle can be recognized. In this case, the rotation angle can be recognized continuously. In addition, it can handle similarly about what converts a rotation angle into an electrical signal.

  Next, in S2, the shooting direction is determined from the rotation angle of the C-arm 5 obtained in S1.

  Here, in S3, the boundary angle can be set as an imaging direction determination condition by an engineer's input. For example, when the boundary angle is θ, as shown in FIG. 52, when the angle θ is “θ = 0 °”, the photographing direction is determined as “CC”, and the angle θ is “−70 ° <θ <0. When “°” or “0 ° <θ <70 °” is satisfied, the photographing direction is determined as “MLO”, and the angle θ is “−90 ° <θ <−70 °” or “70 ° <θ <90 °”. When the condition is satisfied, the shooting direction is determined as “MO”. Note that the range of the angle θ and the types of direction notation characters such as “CC” and “MLO” are given as examples and are not limited thereto.

  Next, the result determined in S4 is written in the item “shooting method” of the accompanying information. Here, when performing special photographing, it is possible to manually input accompanying information in S5 and to correct it.

  As another example of automatic recognition of the rotation angle, as shown in FIG. 53, a first electrode 164 is provided on the rotation shaft 156, and the upper surface of the disk is divided into several places on the C arm support portion 154 side. An electrode (divided electrode) 166 is arranged, a switching action is caused by the positional relationship between the first electrode 164 and the second electrode 166, and angle recognition and determination of the photographing direction are mechanically performed. The imaging direction determination condition is given by the division angle of the second electrode, and information on the imaging direction is written in the accompanying information according to switching.

  In addition, various mechanisms for switching according to the rotation angle are also included.

  When performing special photographing, it is possible to manually input / correct accompanying information through S5.

  Determining whether the breast is the left breast or the right breast, that is, for the item “imaging region” in the accompanying information, press the “right button” or “left button” (both not shown) of the C-arm 5 Is automatically written.

  j. Compression timing adjustment means The means for adjusting the compression timing in association with the X-ray exposure has been described in the description of the X-ray generator 2 and is therefore omitted here.

  k. Biopsy inspection status confirmation means <Confirming biopsy puncture status by X-ray imaging at ultra-low dose> FIG. 54 is a diagram showing a pressure pad used for biopsy inspection. In the biopsy test, the breast is sandwiched between the pressure pads 168 and a sample (specimen) is collected by puncturing a diseased part 172 of the breast through a window 170 provided on the pressure surface of the pressure pad 168.

  Details of the biopsy test up to sample collection will be explained.

  First, the breast is sandwiched between the pressure pads 168. At this time, the diseased part 172 is sandwiched so as to be located in the window 170.

  Next, photographing is performed with the photographing angle set to “0 °”, and it is confirmed that the diseased part 172 is inside the window 170.

  Next, as shown in FIGS. 55 and 56, three-dimensional information is obtained by performing imaging with the C-arm posture (imaging angle) set to “+ 15 °” and “−15 °”.

  Next, the three-dimensional position of the diseased part is calculated from the obtained three-dimensional information, and a double-structure needle 174 is inserted from the window 170 at the calculated position.

  FIG. 57 is a diagram showing how a needle is inserted into a diseased part of a breast.

  Next, imaging is performed with the imaging angle set to “+ 15 °” and “−15 °”, and it is confirmed that the needle is in the center of the diseased part, and a sample is collected.

  Take another shot after collecting the sample to confirm that the diseased sample has been collected.

  When inserting a needle into a diseased part, the needle may be bent. If it can be confirmed whether or not the needle is inserted straight, it is possible to prevent photographing at the time of sample collection while the bent needle is inserted, so that unnecessary exposure to the patient can be avoided.

  Therefore, before taking an image at the time of sample collection, an image is taken with a low-dose X-ray during the needle insertion process to check whether the needle is inserted in the correct posture. In this case, shooting is performed at shooting angles of “+ 15 °” and “−15 °”.

  The dose of X-rays at the time of radiographing may be such that the shape of the needle can be confirmed, so that the dose is smaller than the dose normally performed by fluoroscopy. After confirming the straight movement of the needle in this low-dose shooting, the sample is taken at the time of sample collection. According to the biopsy puncture status confirmation means, it is possible to grasp whether or not the needle has been punctured straight into the diseased part by low-dose X-ray imaging, so that a biopsy test can be appropriately performed without causing unnecessary invasion to the patient.

  l. Biopsy visual field recognition and partial data storage means FIG. 58 is a diagram showing a profile acquisition line set on the detector. On the surface of the detector 42, 176 is a biopsy field, and 178 is a profile acquisition line (ad).

  In the detector, the profile data in each of the profile acquisition lines 178 a to d is collected before all the data, and the profile data of the profile acquisition line “a” and the profile acquisition line “c” is acquired as shown in FIG. To do. Then, the position where the image data exists is detected, for example, as a point A by first-order differentiation of the profile data, and the reading range is determined so as to read only the data in the hatched area (biopsy irradiation field 176) in FIG.

  Note that details of data reading based on the reading range have been described in the description of the X-ray detection apparatus 2, and are omitted here.

  m. Automatic setting of photographing conditions by photographing scene and detector (mode) As a general rule, automatic setting of photographing conditions is performed using Table 1 described above based on the measurement results of various conditions as described above.

  As shown in the operation panel 90 of FIG. 16C, this system can select various system use scenes (imaging scenes) for each examination.

  In this case, the imaging conditions are different between the normal examination, (1) group examination, (2) biopsy, (3) excision specimen examination, and (4) fluoroscopy, and the imaging condition determination table shown in Table 1 is provided for each case. This corresponds to the setting of shooting conditions.

  n. Since it was described in the description of the means X-ray detection apparatus 2 for reading out an image with the end of the exposure as a trigger, it is omitted here.

  o. The patient information output means including the RIS, the identifier (including barcode) means RIS information (for example, examination request information) can be displayed and viewed. When examination request information is selected using the operation panel 90 of FIG. 16 (items for examination request information output are not shown), the requested items regarding the currently selected examination (patient information, examination information, etc. shown in Table 2) ) Is displayed on the screen of the CRT 100 of the output device 10.

  p. Means for enlarging / reducing an image An image is enlarged / reduced by filtering the pixel data of the image. The 1 / n filter is applied when the average value and the maximum value of the pixel values of the n × n matrix are taken assuming n × n, or a predetermined specific matrix element of the n × n matrix is acquired. Applies to cases.

  q. In the initial operation of the CRT / film output selection means system, an output method such as “CRT” or “film” can be selected by the operation panel 90 of FIG.

  r. Means for discriminating whether the abnormality is malignant or benign and outputting the result As a means for determining whether the abnormality is benign or malignant, US Pat. No. 5,133,020 is disclosed for mass shadows. As mentioned above, it can be referred to.

  Here, when the doctor instructs the analysis of the shadow (analysis of the abnormality) on the screen as shown in FIG. 60 at the time of the image interpretation by the doctor, if there is an already detected tumor shadow, whether the shadow is malignant as a computer analysis result? The benign is derived and output. On the other hand, it is output whether or not the portion of the shadow that was pointed out by the doctor directly on the image with the pointing means such as a mouse has been analyzed.

  This system has a mouse as one of input means (instruction means). The mouse is displayed using one surface of the overlay memory 110 of the output device 10, and the clicked position of the mouse button corresponds to the image as the coordinate position of the screen.

  s. The ROI manual input device is a means using a touch panel to output a schema, and is omitted here because it is shown in FIG.

t. Overall Control Program When this system is activated, a screen as shown in FIG.

  The operator can select processing such as “interpretation”, “inspection”, “interpretation after inspection”, and “others” by touching the operation panel.

  The system disk 12 stores the following data in addition to the control program having the functions a to t as described above. Specific items of each data will be described.

(1) The image and the accompanying information image are data having a maximum matrix size of “6000 × 4800” (2 bytes). FIG. 61 is a diagram showing a coordinate system of image data. In normal shooting, a matrix size area of “4800 × 3600” is used.

  As shown in FIG. 62, the coordinate system of the screen is considered separately for the case of a CRT screen (for example, matrix size “2500 × 2000”) and the case of a film (for example, matrix size “8500 × 7000”).

(2) As shown in the inspection history table 7, the inspection history is held as information for searching and reading past images.

 (3) As shown in the inspection request information table 2, the inspection request information obtained from the RIS or the like is held, and the inspection request information created by manually inputting the request information on the paper is also held.

(4) Table for arranging images As shown in Table 5, a table for determining how images are arranged by a doctor is held.

(5) Abnormality detection result table As shown in Table 4, the result detected by the abnormal shadow detection means is held as a table.

(6) Reference image data When the detector 42 is shipped, the detector 42 is irradiated with X-rays for a specified time, and the reference image data is collected and held.

  At the time of maintenance, the difference between the reference data and the image data obtained by trial shooting is taken to detect deterioration of the detector 42 and the like. Next, the memory will be described. The memory 14 is a semiconductor memory, and is a memory for use in operations such as temporarily storing image data and programs and data of the system disk 12. Writing and reading of data to and from the memory 14 is controlled by the central controller 16.

  Central controller 16 controls all operational functions of the system. The operations of the basic system configured as described above are as follows: “Normal examination”, “Group examination”, “Needle biopsy examination”, “Ablation and biopsy examination with a scalpel”, “Follow-up examination”, “Deterioration of detector”, This will be described in the order of “maintenance work”.

  First, operations in a normal examination based on an outpatient examination and interpretation will be described. The most common scene where mammography is used in a normal hospital is an examination and diagnosis for an outpatient who visits the hospital due to an abnormality.

  The operation of the system during inspection and interpretation work will be described below.

  As described above, when the system is activated, the first panel is displayed on the operation panel 90 as shown in FIG.

  From the first panel, one of “interpretation”, “inspection”, and “others” is selected.

  When “interpretation” is selected, an interpreting doctor ID is input, and after the ID is input by the interpreting doctor, the second panel is output to the operation panel 90 as shown in FIG. The ID of the interpreting doctor is stored in the memory 14, and thereafter, output according to the interpretation doctor's preference is performed until the apparatus (system) is brought down.

  Here, for example, it is assumed that the interpretation doctor is Y and ID9876 is input.

  When “inspection” is selected, a third panel is displayed on the operation panel 90 as shown in FIG.

  When “Other” is selected, a fourth panel is displayed on the operation panel 90 as shown in FIG. Set the output conditions on this panel.

  Here, a case where “examination” is selected from the first panel and “normal interpretation” (follow-up interpretation and group examination is the same examination) from the second panel will be described.

(1) Input of patient examination information For example, when an examination request for a patient X is transferred as examination request information from the RIS to the memory 14 of the system, the list of patients including the patient X is operated as shown in FIG. Since it is output as an examination list on the panel 90, the laboratory technician selects the patient X by touching (touching) the portion of the patient X.

(2) Positioning The patient X is positioned (positioned). For the set of imaging devices, it is only necessary to indicate with the arm button which of the left and right breasts is to be imaged (designation of the imaging region). The photographing means (photographing method) is also determined by the inclination of the arm. Information relating to the RIS examination, and information such as the imaging region and imaging method are stored in the image accompanying information.

(3) Breast compression Breast compression applies pressure by a foot switch (not shown). When the specified pressure (10N) is reached, the compression is stopped.

(4) The imaging condition is determined based on the imaging condition determination table in a state where the breast is pressed by the imaging condition setting foot switch. In the imaging condition table, for example, “age: 50 years old, hardness: soft, size: small, thickness: 3 cm” is given as information on the patient X. According to the imaging condition determination table, for example, an imaging condition “filter: Mo, kvp: 28 kvp, mA: 10 mA” is obtained.

(5) X-ray exposure X-ray exposure is controlled under the above-described imaging conditions, and X-ray exposure is performed at the discretion of an engineer. The exposure time is managed by the AEC 30, and imaging is performed with an appropriate mAs value. Appropriate pressure is applied to the patient's breast only during exposure according to the technician's settings. For example, when the engineer determines that another 1N load is to be applied and inputs that value, a total pressure of 11N is applied to the breast only during the exposure time, and the pressure is released simultaneously with the end of the exposure. A pressure exceeding the ACR standard is set in advance, and it is a safety mechanism that does not give an excessive pressure beyond that.

ここで、フィルムを用いて読影する場合について説明する。 (6) The image data obtained from the storage detector 42 in association with the image and the accompanying information is temporarily stored in the memory 14. Image accompanying information is created based on this data and stored in the memory 14 in association with the image data. Table 8 shows an example of the image accompanying information.

Here, the case of interpretation using a film will be described.

  Interpretation using a film includes a case where the CRT 100 is used as an auxiliary and a case where the interpretation is performed using only the film. When the CRT 100 is used supplementarily, the output of the film is simply a density correction. These outputs are sequentially performed after one set of inspections. The following operations are performed inside the system.

(1) Image data on the image reading memory 14 is read one by one.

(2) The density correction processing function is activated for the density-corrected image to correct for proper exposure. The image data subjected to exposure correction is stored in the memory 14.

(3) CAD processing CAD processing is not performed when the CRT 100 is used in an auxiliary manner.

  First, an abnormal shadow detecting means is applied to the image data after the image density correction. As shown in FIG. 63, it is assumed that the microcalcification shadow 180 is detected at the position of coordinates (1000, 1500) and the tumor shadow 182 is detected at the position of coordinates (2000, 3000). The detection result is described in the above-described abnormality detection result table (Table 4) and stored in the memory 14.

(4) Image processing Image processing is not performed when the CRT 100 is used in an auxiliary manner.

  “1000 × 1000” ROI data centered on the coordinates (1000, 1500) and coordinates (2000, 2000) of the image is extracted from the abnormality detection result table created in the CAD process described above. If the abnormal position is included in the ROI, the previously extracted data is used as the ROI data. Further, these ROI data are processed by the image processing function and stored in the memory 14 again. Image processing corresponding to the shadow such as unsharp masking processing is performed on the microcalcification shadow 180 and lookup table is changed on the tumor shadow.

(5) Screen creation The position where the image coordinates (1000, 1500) are converted to the screen coordinates based on the abnormality detection result table created in the above-described CAD processing, that is, a mark indicating the position of the microcalcification shadow is shown in the outer frame of the image. And a mark indicating the position of the tumor shadow is set in the outer frame of the image at a position obtained by converting the image coordinates (2000, 3000) to the screen coordinates. Further, as shown in FIG. 64, an image obtained by enlarging the size of one pixel twice as much as ROI data is arranged next to the image. These screen data are sent to the laser writing device 118.

  When the CRT 100 is used in an auxiliary manner, for the image interpretation doctor Y, for example, the arrangement of images is determined according to Table 6 already shown, a screen in which only the images are arranged is created, and the data is sent to the laser writing device 118.

(6) Film printing Screen data obtained by the above-described image processing is sent to the laser writing device 118, and an instruction is given to print on the film. Next, an operation when performing (support) diagnosis using CRT will be described.

(1) A list of patients who have completed the examination is displayed on the examination information input operation panel 90. Here, the examination of patient X is selected.

(2) Image data on the image reading memory 14 is read one by one.

(3) The density correction processing function is activated for the density-corrected image to correct for proper exposure. The image data subjected to exposure correction is stored in the memory 14.

(4) CAD processing An abnormal shadow detecting means is applied to the image data after image density correction. As shown in FIG. 63, it is assumed that the microcalcification shadow 180 is detected at the position of coordinates (1000, 1500) and the tumor shadow 182 is detected at the position of coordinates (2000, 3000). The detection result is described in the above-described abnormality detection result table (Table 4) and stored in the memory 14.

(5) Image processing Image processing is not performed when the CRT 100 is used in an auxiliary manner.

  “1000 × 1000” ROI data centered on the coordinates (1000, 1500) and the coordinates (2000, 2000) of the image is extracted from the abnormality detection result table (Table 4) created in the CAD process described above. If the abnormal position is included in the ROI, the previously extracted data is used as the ROI data. Further, these ROI data are processed by the image processing function and stored in the memory 14 again. Image processing corresponding to the shadow such as unsharp masking processing is performed on the microcalcification shadow 180 and lookup table is changed on the tumor shadow.

(6) Screen creation and display Interpretation An initial screen is displayed on the operation panel according to an instruction from the doctor Y. The attention image is selected on the initial screen, and the display abnormal shadow detection result and the abnormal shadow gaze are displayed.

  FIG. 65 is a diagram showing an initial screen displayed on the operation panel.

  All the images of the examination are displayed by the preferred arrangement method of the interpretation doctor Y until the examination is completed. In addition, an image that needs to be reduced in display is reduced and displayed.

  The initial screen has a switch that abstracts (deforms) the image, and the target image is selected by the switch. In addition, a switch used for displaying the abnormal shadow detection result and a switch used for gazing (enlarging and emphasizing) the abnormal shadow are provided.

  As the attention image, only the image selected on the operation panel of the initial screen is displayed.

  As shown in FIG. 66, the abnormal shadow detection result is displayed superimposed on the displayed image. An abnormal shadow indication mark is created on the overlay memory by creating a micro-calcified shadow mark at coordinates (1000, 1500) and a tumor shadow mark at coordinates (2000, 3000). Overlapping display.

  In the abnormal shadow gaze, the ROI data created by the image processing of (5) based on the priority is displayed on the displayed image without being reduced.

Table 9 is a table showing the priority of gaze for abnormal shadows.

  67A and 67B are views showing ROI display and CRT display on the operation panel. FIG. 67A shows the display of the CRT, and FIG. 67B shows the display of the operation panel 90.

  On the operation panel 90, the position of the ROI displayed on the CRT on the image is abstracted (deformed) and displayed.

  Next, the operation in group screening will be described.

  The contents of the examination at the mass examination are the same as the examination flow of the normal examination described above. If the diagnosis is only for the film, it is the same as the interpretation by the film for the normal inspection. In the case of group screening, examination and film output are performed together, and interpretation is also performed later.

  Assume that all inspection results (image data, etc.) are all stored in the hard disk. The operation flow of the system in the interpretation work in such a case will be described below.

(1) A list of patients who have completed the examination is displayed on the examination information input panel. Here, the examination of patient X is selected.

(2) Read image data of the patient X on the image reading memory 14 one by one. A density correction processing function is activated for the image and corrected to an appropriate exposure. The image data subjected to exposure correction is stored in the memory 14. Abnormal shadow detection means is applied to the corrected image data. As shown in FIG. 63, it is assumed that the microcalcification shadow 180 is detected at the position of coordinates (1000, 1500) and the tumor shadow 182 is detected at the position of coordinates (2000, 3000). The detection result is described in the above-described abnormality detection result table (Table 4) and stored in the memory 14.

(3) “1000 × 1000” ROI is set by the ROI position determination means set by the image processing ROI setting shuttle, and ROI data is obtained in real time.

(4) Image processing ROI data is processed by the image processing function and stored in the memory 14 again. Image processing corresponding to the shadow such as unsharp masking processing is performed on the microcalcification shadow 180 and the look-up table is changed on the tumor shadow 182.

(5) Screen creation The initial screen is displayed on the operation panel 90 according to the instruction of the interpreting doctor Y. The target image is selected on the initial screen, and the display result of the abnormal shadow detection, the abnormal shadow gaze, and the gaze position by the shuttle are displayed.

  As shown in FIG. 65, an initial screen is displayed on the operation panel 90. All images of the examination are displayed by the preferred arrangement method of the interpreting doctor Y until the examination is completed. In addition, an image that needs to be reduced in display is reduced and displayed.

  The initial screen has a switch that abstracts (deforms) the image, and the target image is selected by the switch. In addition, a switch used for displaying the abnormal shadow detection result and a switch used for gazing (enlarging and emphasizing) the abnormal shadow are provided.

  As the attention image, only the image selected on the operation panel of the initial screen is displayed.

  As shown in FIG. 66, the abnormal shadow detection result is displayed so as to overlap the displayed image. An abnormal shadow indication mark is created on the overlay memory with a microcalcified shadow mark at the coordinates (1000, 1500) and a tumor shadow mark at the coordinates (2000, 3000), and is overlaid on the image by the image display manager. To display. In the abnormal shadow gaze, the ROI data created on the basis of the priorities shown in Table 9 is displayed for the displayed image without reducing it.

  The gaze position displayed by the shuttle is displayed without reducing the generated ROI data instructed by the shuttle.

  67A and 67B are views showing ROI display and CRT display on the operation panel. FIG. 67A shows the display of the CRT, and FIG. 67B shows the display of the operation panel 90.

  On the operation panel 90, the position of the ROI displayed on the CRT on the image is abstracted (deformed) and displayed.

  Next, the operation in the needle biopsy test will be described.

  If an abnormal shadow is found as a result of the mammogram interpretation, a biopsy is performed to determine whether the shadow is malignant or benign if necessary by the judgment of the doctor. The purpose of this test is to insert a needle into the lesion and take out abnormal cells.

  Operations in such case inspection and interpretation work will be described below.

  In this case, “Biopsy” is selected on the third panel of the operation panel 90 as shown in FIG. In FIG. 16C, “biopsy” can also be selected. In this case, X-ray fluoroscopy is performed without performing X-ray imaging. Similar to inspection.

(1) X-ray exposure is performed under the conditions of X-ray exposure biopsy.

  The small field of view for biopsy is judged and the image is written in the memory 14.

  X-rays are irradiated at different angles and stored in the memory 14 in the same manner.

(2) Image reading Two images are taken out from the memory 14.

(3) Creation of Screen for Biopsy Examination As shown in FIG. 68, a screen in which two images are arranged is created and displayed on the CRT 100.

(4) Shading instruction A shadow is instructed for two images by the mouse, and the instructed position is stored in the memory 14.

(5) Calculate the puncture distance from the shadow position The distance is calculated by the biopsy puncture position calculation means.

(6) Puncture distance output The puncture distance is displayed on the CRT screen or on the panel. In order to confirm the biopsy puncture status, confirmation imaging is performed with ultra-low dose X-rays. The exposure is performed and the image is stored in the memory 14 as in the puncture distance calculation. In addition, the shadow instruction position at the time of puncture distance calculation is shown in the overlay memory 110 and displayed superimposed on the image. Next, the operation in the excision / biopsy test with a scalpel will be described.

  In the biopsy (biopsy test) described above, if the lesion is excised with a scalpel, the state of the lesion can be observed most reliably. However, the invasion to the patient is very large.

  When performing such inspection, mammography is mainly used for confirmation work. The operation of the system in the interpretation work will be described below.

  “Biopsy” is selected on the third panel of the operation panel 90.

(1) Setting of excised specimen Set excised specimen.

(2) X-ray exposure is performed under the X-ray irradiation excision specimen imaging conditions.

(3) Image storage The image is stored in the memory 14.

(4) Image readout and density correction The image is read out from the memory 14 and the image density is corrected as described above.

(5) CRT display As shown in FIG. 69, an image of the excised specimen 300 is displayed on the CRT 100. Next, an operation in interpretation for follow-up will be described.

  When the inspection is regularly performed, past inspection data is used for comparison. The operation of the system in such interpretation work will be described below.

  “Follow-up interpretation” is selected on the second panel of the operation panel 90.

(1) A list of patients who have completed the examination is displayed on the examination information input panel. Patient X is selected.

(2) Obtain past examination data from the database or PACS.

A past examination of the patient X is selected from the examination history, searched in the data base, and the image is transferred to the memory 14. It is assumed that an unread image is already stored in the memory 14.

(3) When the screen creation CRT 100 is used in an auxiliary manner, the arrangement of images for the interpretation doctor Y is determined according to Table 5, and a screen in which the uninterpreted image and the past image are arranged as shown in FIG. 70 is created. To the laser writing device 110. In addition, the detection by the abnormal shadow detecting means may be performed on the unread image as in the case of normal reading. As shown in FIG. 71, the result may be output only when no abnormality is detected in the past image and when an abnormality is detected in the unread image.

(5) CRT output or film output (3) A screen created by screen creation is output to the CRT 100 or the film 102.

  Next, the operation when performing maintenance work corresponding to detector deterioration will be described.

  In order to keep the quality of the mammogram constant at a high level, it is often necessary to perform maintenance on the equipment. The following two cases will be described with respect to the operation of the work system that allows easy and highly accurate maintenance of the detector 42 that affects the imaging performance. The maintenance of the detector 42 includes automatic maintenance performed every time the system is activated and maintenance performed by a user (photographer) at an appropriate interval.

  In automatic maintenance performed every time the system is started, first, the image data on the detector 42 is reset, and dark image data is collected. The dark image data is obtained by leaving the X-rays unexposed for a certain period of time. After resetting, X-ray exposure data is collected by exposing X-rays for a certain period of time. A difference between pixel values of the collected X-ray exposure data and dark data is obtained, and a pixel having a difference greater than or equal to a certain value is determined as a scratch. When a flaw is detected, if the flaw is a single one, the data of adjacent pixels is corrected as it is as the pixel value. If the scratch exceeds a certain value, it is determined that the deterioration is large, and a warning mark or the like is displayed on the CRT 100 or the operation panel 90. In maintenance performed by the user (photographer) at an appropriate interval, first, “maintenance” is selected on the fourth panel as shown in FIG. Next, X-rays are subjected to test exposure under test conditions, and the obtained data is stored in the memory 14. A reference image is stored in advance in the system disk 12, and a difference between the data obtained by the X-ray test exposure and the reference image is obtained. If the difference is a pixel having a certain value or more, this is determined as a scratch. Correction is performed in the case of a single flaw or the like, and the data of adjacent pixels is used as the pixel value as it is. If the scratch exceeds a certain value, it is determined that the deterioration is large, and a warning mark or the like is displayed on the CRT 100 or the operation panel 90. Next, a case where PACS is used will be described.

  When information such as patient information or examination information is obtained from an external system, for example, RIS data from the RIS is transferred to the PACS system via the gateway.

  When interpreting a mammogram image using a general-purpose workstation, the general-purpose workstation has a mammogram interpretation function as one application.

(Embodiment 2) Next, a second embodiment will be described. In the second embodiment, a system in which a network function is applied to a basic system (referred to as a modality system) will be described.

  FIG. 72 is a block diagram showing an apparatus configuration of the modality system. The modality system has a configuration in which a mammography photographing apparatus 210, a digitizer 220, an imager 230, a database 240, and a mammogram interpretation workstation 250 are connected to each other via a local area network (hereinafter abbreviated as LAN) 200. It has become. The LAN 200 has a function of transferring data and commands input / output between devices at high speed.

  The difference between the modality system and the basic system of the first embodiment is that the image photographing system and the image output system are distributed via a network. Therefore, the output device 10 in the basic system is not provided in this system. The CRT 260 is merely for confirming a captured image, and the captured image is interpreted by the mammogram interpretation workstation 250. Further, the imager 230 outputs the filmed image to the film.

  FIG. 73 is a block diagram showing an internal configuration of the mammography photographing apparatus 210. As shown in FIG. The mammography apparatus 210 includes an X-ray generator 211, an X-ray detector 212, an input device 213, an RIS (I / F) unit 214, a memory 215, a ROM 216, an optical disk 217, a LAN I / F unit 218, and a control device 219. The image confirmation CRT 260 is connected.

  The X-ray generator 211 and the X-ray detector 212 are the same as those in the first embodiment. Further, the mammography imaging apparatus 210 includes an optical disk 213 that holds image data and the like obtained by the X-ray detection apparatus 211. As a result, it is possible to transfer the image data offline without using the LAN 200.

  Data from the RIS is input to the present system by the RISI / F unit 8.

  Note that the photographing confirmation CRT 211 confirms an image immediately after photographing, and corrects the image density.

  FIG. 74 is a block diagram showing an internal configuration of the digitizer 220. As shown in FIG. The digitizer 220 includes a film feed / laser irradiation control unit 221, a data reading unit 222, an input device 223, a memory 224, a ROM 225, a LAN I / F unit 226, and a control device 227.

  The film feed / laser irradiation control unit 221 and the data reading unit 222 digitize analog film data that has not been digitized such as past images. The digitized data is transferred from the data reading unit 222 to the LAN 200 via the memory 224 and the LAN I / F unit 226.

  The input device 223 has a function of inputting identification information for identifying a film to be input.

  FIG. 75 is a block diagram showing an internal configuration of the imager 230. The imager 230 includes a film feed / laser irradiation / film development control unit 231, a data writing unit 232, an input device 233, a memory 234, a ROM 235, a LAN I / F unit 236, and a control device 237.

  The imager 230 receives image data from the LAN 200 and outputs it to the film. The image data is sent from the LAN 200 to the data writing unit 232 via the LAN I / F unit 236 and the memory 234. The data writing unit 232 sends the image data to the film feed / laser irradiation / film development control unit 231 and controls writing on the film.

  The film feed / laser irradiation / film development control unit 231 writes image data to the film by laser, develops the film, and discharges the film. Very high definition can be drawn on the film. The beam diameter of the laser for writing on the film is arbitrarily changed, and the screen data is written in accordance with the size of the film.

  FIG. 76 is a block diagram showing the internal configuration of the database 240. The database 240 includes an optical disk 242, a hard disk 243, a memory 241, a ROM 244, a LAN I / F unit 245, and a control device 246.

  The database 240 stores past images and other inspection images on the hard disk 243 or the optical disk 242 of the optical disk changer. The stored image can be searched from the hard disk 243 or the optical disk 242 of the optical disk changer by using the patient name (patient ID) as a key by the ROM 244. The searched image is transferred to the LAN 200 via the memory 241 and the LAN I / F unit 245, and the LAN 200 further transfers this to an external device.

  FIG. 77 is a block diagram showing the internal configuration of the mammogram interpretation workstation 250. The mammogram interpretation workstation 250 includes a LAN I / F unit 251, a system disk 252, an input device 253, a memory 254, a CRT 255, and a control device 256.

  The mammogram interpretation workstation 250 has a function equivalent to that of the operation panel 90 described in the first embodiment, and outputs a mammogram image for interpretation and a function for inputting an instruction from the operator via a touch screen. It has a function.

  The system disk 252 is the same as the system disk 12 described in the first embodiment, includes various control programs, and executes various functions such as image processing by the control programs.

  As described above, according to the second embodiment, since the network function is added to the basic system, the image capturing system and the image output system can be configured separately, and the load in the system can be distributed. . It is also easy to add another device or replace a device with a device with higher performance.

(Embodiment 3) Next, a third embodiment will be described.

  In the third embodiment, a system in which PACS is applied to a basic system (referred to as a PACS system) will be described.

  FIG. 78 is a block diagram showing a device configuration of the PACS system. The PACS system includes a mammography apparatus 280, a gateway 281, a gateway 282, a digitizer 283, an imager 284, a database 285, and a workstation 286.

  The mammography photographing device 280, the digitizer 283, the imager 284, and the database 285 are devices equivalent to the above-described modality system. On the other hand, the workstation 286 is not a dedicated device for handling mammogram images, unlike the interpretation workstation 250 of the above-described modality system.

  The CRT 287 is a device for image confirmation, and the mammogram image is read by the workstation 286.

  Unlike the above-described modality system, the PACS system can be connected to another modality 288 via the gateway 281. Also, information from the RIS 289 such as inspection request information is temporarily input to the PACS system via the gateway 282.

(Embodiment 4) Next, a fourth embodiment will be described. In the fourth embodiment, other system variations will be described.

  FIG. 79 is a block diagram showing a schematic configuration of an abnormality detection (diagnosis support) system. The abnormality detection system digitizes an analog film by a digitizer 260 and detects an abnormal shadow by a workstation 262.

  The detected abnormal shadow is output to the CRT 268 or the imager 264. When configured as described above, the system becomes simple.

  The simplest system that does not indicate the detected abnormal position and simply emits a warning sound is also conceivable.

  FIG. 80 is a block diagram illustrating a schematic configuration of the imaging system. The photographing system includes a mammography photographing device 270, an imager 272, and a CRT 274. The photographing system has only a function of correcting and outputting the density of the photographed image, and the handling is the same as the conventional screen / film system.

  The present invention is not limited to the above-described embodiments, and various modifications can be made. For example, the arrangement of images is the same when an abnormality is detected in one of the images taken in the “CC” or “ML” direction, for example, when detected in the “CC” image. The “ML” images of the parts may be displayed side by side. For example, when the “ML” images are detected, the “CC” images of the same part may be displayed side by side.

  Further, when displaying the detection result of the abnormal shadow by CAD, even when the “CC” image and the “ML” image are displayed, it may be output when an abnormality is detected. Alternatively, an image indicating that an abnormal shadow is pointed out may be created next to the original image (mammogram image) and displayed superimposed on the original image. In that case, the size of the superimposed image is the same as or smaller than that of the original image. Moreover, you may make it output the character information to the effect of pointing out an abnormal shadow next to an original image or a process image.

1 is a block diagram showing a schematic configuration of a basic system according to a first embodiment of a mammography apparatus according to the present invention. FIG. 3 is a perspective view showing an appearance of the basic system 1. FIG. 3 is a block diagram schematically showing an internal configuration of the X-ray generator 2. The figure which shows the characteristic for determining the hardness of a breast. The figure for demonstrating the magnitude | size detection of a breast. The figure which shows an example of the operation panel for selecting the magnitude | size of a film. The figure which shows the data collection point for AEC in a plane detector. The figure which shows the detector 46 for AEC for collecting AEC data, without performing destructive reading of detector data. Sectional drawing which looked at the mechanism part which presses a breast with the compression board 3 from the side. The figure which shows an example of the drive method of the compression part. The block diagram which shows schematic structure of a breast compression mechanism. The figure which shows the process of compressing a breast in relation to X-ray exposure. The figure which shows the process of compressing a breast in relation to X-ray exposure. FIG. 3 is a block diagram schematically showing an internal configuration of the X-ray detection apparatus 4. The circuit diagram which shows the structure of a TFT plane detector. The figure showing the screen transition of the operation panel 90. FIG. The figure which shows the test | inspection (patient) list panel displayed on the operation panel. The figure which shows the operation panel which performs the input for output screen control. The perspective view of the panel for image selection. The perspective view of the panel for selection of detailed display ROI. The figure which shows an interpretation doctor ID input panel. FIG. 3 is a block diagram showing an internal configuration of the output device 10. The figure which shows an example of the output film. The figure which shows the histogram of a normal breast (breast). The figure which shows the histogram of a breast (dense breast) where a mammary gland area | region is dense. The figure which shows the micro area | region of n pixel x n pixel. The figure showing the relationship between a pixel value and a gray scale (luminance). The figure which shows schematically the flow until it displays or outputs the image of a breast on either side. The figure which shows the specific example of a process of the density | concentration equalization processing unit. The figure which shows the ROI for an enlarged display, and the locus | trajectory of the position movement of ROI center. The figure which shows a locus | trajectory when the position movement of ROI center is performed continuously. The figure which shows a mode that the breast outline 138 is approximated by a polygon. The figure which shows the example of the enlarged display by set ROI133. The figure which shows the example of the contrast emphasis by set ROI133. The figure which shows the locus | trajectory of ROI position movement according to various mammogram images. The figure which shows the relationship between a pixel value and a gray scale. The figure which shows a breast area. The figure for calculating | requiring the outline angle 144. FIG. The figure which showed the kind of imaging | photography direction. The figure which shows the classification of the arrangement method of the image on the screen. The figure which showed the mode of arrangement | positioning of the image of the doctor A. FIG. The figure which showed the mode of arrangement | positioning of the image of the doctor B. FIG. The figure which showed the mode of arrangement | positioning of the image of the doctor C. FIG. The figure which shows the size process of image data. The schematic diagram of the screen which showed the abnormal shadow detection result from the exterior of the image. The figure which shows a mode that the image of this time and the last image (past image) are each arrange | positioned on the screen of two CRT. The figure for demonstrating contrast adjustment. The figure which shows the screen which displayed the abnormal shadow. The figure which looked at C arm and C arm support part from the side. The block diagram which shows roughly the process which recognizes the imaging | photography method automatically. The perspective view which shows the outline of the mechanism which recognizes a rotation angle automatically. The figure which shows the judgment method of imaging conditions. The figure which shows the other example of the automatic recognition of a rotation angle. The figure which shows the pressure pad used for a biopsy inspection. The figure which shows the attitude | position of C arm roughly. The external view which shows the attitude | position of C arm. The figure which showed a mode that the needle | hook is inserted in the diseased part of a breast. The figure which shows the profile acquisition line set on the detector. The figure which shows profile acquisition line "a" and profile acquisition line "c". The figure which shows the screen for a doctor to instruct | indicate the analysis of a shadow (analysis of abnormality). The figure which shows the coordinate system of image data. The figure which shows the coordinate system of CRT and a film. The figure which shows the coordinate of the detected microcalcification shadow and the mass shadow. The figure which shows the screen on which the CAD result and the ROI of enlarged display were displayed. The figure which shows the initial screen displayed on the operation panel. The figure which shows the screen which displayed the abnormal shadow detection result superimposed on the image. The figure which shows the display of ROI and the display of CRT in an operation panel. The figure which shows the screen which displayed the image of 2 sheets side by side. The figure which shows the image of a resected specimen. The figure which shows the screen which arranged the unread image and the past image. The figure which shows the screen which arranged the unread image and the past image in which the abnormal shadow was output. The block diagram which shows schematic structure of the modality system which concerns on 2nd Example of the mammography apparatus by this invention. 2 is a block diagram showing an internal configuration of a mammography photographing apparatus 210. FIG. 2 is a block diagram showing an internal configuration of a digitizer 220. FIG. FIG. 2 is a block diagram showing an internal configuration of an imager 230. The block diagram which shows the internal structure of the database 240. FIG. The block diagram which shows the internal structure of the mammogram interpretation workstation 250. FIG. The block diagram which shows schematic structure of the PACS system which concerns on 3rd Example of the mammography apparatus by this invention. The block diagram which shows schematic structure of the abnormality detection (diagnosis assistance) system which concerns on 4th Example of the mammography apparatus by this invention. The block diagram which shows schematic structure of the imaging | photography system which concerns on 4th Example of the mammography imaging device by this invention. The block diagram which shows schematic structure of the conventional PACS system.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Basic system, 2 ... X-ray generator, 3 ... Compression board, 4 ... X-ray detection device, 5 ... C arm, 6 ... Input device, 8 ... RISI / F part, 10 ... Output device, 12 ... System Disc, 14 ... Memory, 16 ... Central processing unit, 18 ... Bar code reader, 20 ... X-ray tube, 22 ... High pressure generator, 24 ... X-ray controller, 26 ... Filter switching unit, 28 ... Compression pressure control unit, 30 ... AEC, 32 ... Photo sensor, 34 ... Control panel, 36 ... Thickness data, 38 ... Optical detector, 39 ... Light, 40 ... Reflector, 42 ... Flat detector, 44 ... Data collection point, 48 ... Compression , 49 ... compression plate support, 50 ... pressure sensor, 52 ... control unit, 54 ... movable part, 56 ... set value, 60 ... read time setting device, 62 ... timing generator, 64 ... drive device, 68 ... read out Equipment, 70 A / D conversion unit, 72 ... read range setting device, 73 ... array, 76 ... gate line, 78 ... data line, 80 ... FET, 82 ... sensor, 90 ... operation panel, 92 ... schema, 94 ... image selection panel 95 ... Mechanical switch, 96 ... Detailed display ROI selection panel, 98 ... ID input device, 100 ... CRT, 102 ... Film, 104 ... Image reduction / enlargement processing unit, 106 ... Screen creation unit, 108 ... Frame memory, DESCRIPTION OF SYMBOLS 110 ... Overlay memory, 112 ... Display management part, 114 ... D / A conversion part, 116 ... Bar code production | generation part, 118 ... Laser writing apparatus, 120 ... Bar code, 122 ... ROI, 124 ... Image data, 126 ... Before conversion 128 ... straight line after change, 129 ... image memory bank, 130 ... density equalization unit, 132 ... composite image, 1 DESCRIPTION OF SYMBOLS 3 ... ROI, 134 ... Average value calculation part, 135 ... Dividing part, 136 ... Image calculating part, 137 ... Outline part, 138 ... Breast outline, 139 ... 1st closed curve, 140 ... 2nd closed curve, 145 ... Screen, 146 ... Mammogram image, 147 ... Marker, 148 ... Abnormality (shadow), 149 ... Number of detected anomalies, 150 ... Other markers, 152 ... Identifier, 154 ... C arm support, S1 ... C arm angle recognition processing , S2 ... Shooting direction determination process, S3 ... Determination condition input process, S4 ... Accompanying information writing process, S5 ... Manual input / correction process, 156 ... Rotating shaft, 158 ... First gear, 160 ... Second gear DESCRIPTION OF SYMBOLS 164 ... 1st electrode, 166 ... 2nd electrode, 168 ... Pressure pad, 170 ... Window, 172 ... Disease part, 174 ... Needle, 176 ... Biopsy irradiation field, 178 ... Profile acquisition line 180 ... microcalcification shadow, 300 ... resection specimen.

Claims (7)

  An input means for inputting a mammogram image;
  Setting means for setting a closed curve based on the breast contour and a region of interest of a predetermined shape on the mammogram image input by the input means;
  Moving means for moving the region of interest to a plurality of different positions according to the closed curve;
  Image processing means for performing predetermined image processing on image data corresponding to the region of interest at each of the plurality of different positions, and generating a plurality of display images corresponding to the region of interest at the plurality of different positions; ,
  Display means for displaying the plurality of display images;
  A mammography apparatus comprising: The mammography apparatus according to claim 1, wherein the image processing unit performs at least one of enlargement processing, contrast enhancement processing, and frequency enhancement processing as the image processing .   The setting means sets a plurality of different closed curves so that a region in which the region of interest moves along the closed curve covers all of the subject regions on the mammogram image. 2. The mammography apparatus according to 2.   4. The mammography apparatus according to claim 1, further comprising changing means for changing the shape of the closed curve. A detecting means for detecting an abnormal shadow from a mammogram image input by the input means;
The mammography apparatus according to claim 1 , wherein the setting unit sets the closed curve so that a region in which the region of interest moves along the closed curve covers a position corresponding to the abnormal shadow . The mammography apparatus according to claim 5, wherein the moving unit moves the region of interest so that a position corresponding to the abnormal shadow is a center of the region of interest .   The image processing means performs the image processing including at least one of enlargement processing, contrast enhancement processing, and frequency enhancement processing according to the detected abnormal shadow detection result. The mammography apparatus according to 1.

Images