JP2009077780A - Breast examination system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a breast examination system which carries out an appropriate breast examination by comparative diagnostic reading. <P>SOLUTION: The breast examination system generates and displays a mammographic image and an ultrasonic image. An image processing apparatus 13 of the breast examination system includes a virtual mammographic image generating section 132 that generates a virtual mammographic image, which is a pseudo compressed image, by deforming an ultrasonic three-dimensional volume data, and a display control section 133 for controlling display of the mammographic image and the virtual mammographic image. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a breast examination system that displays a mammography image and an ultrasound image.

  In order to diagnose cancer and other abnormalities, a mammography method (mammography) in which a breast examination is performed by providing a two-dimensional image of breast tissue is widely used. Since the breast has a three-dimensional and delicate structure, imaging is performed with a dedicated X-ray apparatus.

  A general X-ray apparatus uses strong (hard) X-rays to project hard objects such as bones. On the other hand, an X-ray apparatus used in a breast examination uses weak (soft) X-rays because soft tissues such as fat and mammary glands are targeted. At the same time, the breast examination is the only examination in which the skin is in direct contact with the machine, so various considerations have been made.

  Mammography is performed while pulling and compressing the breast. The imaging is performed from two directions, for example, MLO (medial-oblique: inward / outward oblique direction) and CC (cranial-caudal view: head-to-tail direction).

  However, there is an essential limitation in that a mammography image acquired by mammography can only provide a planar image of a three-dimensional object. Even if a potential area indicating medical interest is pointed out on the mammography image, the upper side and the inner side of the target area may not be determined in the two-dimensional image of the breast. Thus, digital X-ray imagers provide full field or nearly full field imaging. Completing the diagnosis may require alternative means such as biopsy and complementary imaging techniques and diagnosis.

  The main complementary imaging techniques for mammography are ultrasound imaging and magnetic resonance imaging (MRI), both of which have the advantage of not using ionizing radiation. The main advantage of ultrasound is that ultrasound imaging is relatively inexpensive and that ultrasound imaging works well with dense breasts that are difficult with mammography. Furthermore, ultrasound imaging plays an important role as a guide for needle biopsy.

  In recent years, for breast cancer screening, combined screening with mammography and ultrasonic imaging has become widespread. As the number of breast cancer patients continues to increase, it is expected that more complete screening will be conducted.

In addition, as a well-known document relevant to this application, there exist the following, for example.
JP 2005-125080 A

  However, when a mammography image captured in a compressed state while compressing a breast is compared with an ultrasound image captured in a non-compressed state, the shape of the breast at the time of imaging does not match. Therefore, comparative interpretation of mammography images and ultrasound images has required difficulty for doctors' interpretation techniques.

  In addition, since the mammography image and the ultrasonic image are not associated with each other, the position of the micro limestone displayed on the mammography image is not known on the ultrasonic image.

  The present invention has been made in view of the above-described circumstances, and an object thereof is to provide a breast inspection system capable of realizing an appropriate breast inspection by comparative interpretation.

  In order to solve the above-described problems, a breast examination system according to the present invention is a pseudo-compression that transforms three-dimensional volume data of ultrasound in a breast examination system that generates and displays a mammography image and an ultrasound image. A virtual mammography image generation unit that generates a virtual mammography image that is an image; and a display control unit that controls display of the mammography image and the virtual mammography image.

  According to the breast examination apparatus according to the present invention, an appropriate breast examination by comparative interpretation can be realized.

  An embodiment of a breast examination system according to the present invention will be described with reference to the accompanying drawings.

  FIG. 1 is a conceptual diagram illustrating an embodiment of a breast examination system.

  FIG. 1 shows a breast examination system 10 according to the present embodiment. The breast examination system 10 includes a three-dimensional ultrasonic image diagnostic apparatus 11, a mammography apparatus 12, and an image processing apparatus 13, and the three-dimensional ultrasonic image diagnostic apparatus. 11, the mammography apparatus 12 and the image processing apparatus 13 are connected to each other via a network N such as a hospital backbone LAN (local area network). The breast examination system 10 deforms the breast three-dimensional volume data generated by the three-dimensional ultrasound image diagnostic apparatus 11, generates a virtual mammography image that is a pseudo compression image, and converts the mammography image and the virtual mammography image into a virtual mammography image. It is also displayed.

  The three-dimensional ultrasonic image diagnostic apparatus 11 performs complementary mammography imaging. The three-dimensional ultrasonic diagnostic imaging apparatus 11 is an apparatus for realizing a water immersion method, which is a technique devised mainly for mass screening in ultrasonic examination of the breast. In the water immersion method, one or both of the breasts of a patient is immersed in a gantry containing water, and image data is generated while moving an ultrasonic probe facing the patient across the gantry. It is. The ultrasonic probe can be moved automatically using a mechanical moving stage, and because the whole breast can be imaged through water in the gantry, it is suitable as a mass screening system. is there.

  The mammography apparatus 12 executes mammography imaging while pulling and compressing the breast, and generates a mammography image.

  The image processing apparatus 13 is a workstation configured based on a computer. The image processing device 13 deforms the breast three-dimensional volume data generated by the three-dimensional ultrasound image diagnostic device 11 to generate a virtual mammography image that is a pseudo compression image.

  FIG. 2 is a block diagram showing a hardware configuration of the three-dimensional ultrasonic image diagnostic apparatus 11.

  As shown in FIG. 2, the three-dimensional ultrasonic diagnostic imaging apparatus 11 is mainly composed of an ultrasonic probe 21, a bed apparatus 22 and an apparatus main body 23.

  The ultrasonic probe 21 transmits and receives ultrasonic waves by disposing a plurality of ultrasonic transducers at the tip portion. The ultrasonic transducer is an electroacoustic transducer, and converts an electrical pulse into an ultrasonic pulse when transmitting an ultrasonic wave, and converts an ultrasonic signal into an electric signal when receiving an ultrasonic wave. The ultrasonic probe 21 is a one-dimensional (single row with only azimuth steering) array probe, a 1.5-dimensional array (electronically focused but not steered to the elevation dimension) probe, two-dimensional, depending on the array transducer system. It is classified as an array (fine pitch array with extensive 3D steering) probe. Among these, in order to actively acquire biological volume data, it is desirable to employ a two-dimensional array probe.

  Moreover, even if the ultrasonic probe 21 is a one-dimensional array probe or a two-dimensional array probe, the ultrasonic probe 21 itself has a rocking function, and acquires a plurality of tomographic images while changing the scan section one after another. Alternatively, it may be a mechanical three-dimensional probe that acquires volume data.

  The couch device 22 includes a top plate 22a on which the patient P is placed in the prone position (prone position), and a gantry 22b for storing water and storing the breast of the patient P. The gantry 22b has a rectangular shape with adjacent anti-lateral edges (X-axis direction) and abdomen-side edges (Y-axis direction) orthogonal to each other on the top surface of the top plate 22a in the depth direction (Z-axis direction). It is given as a space formed by extending.

  FIG. 3 is a schematic diagram showing the configuration of the gantry 22b.

  As shown in FIG. 3, the point where the Anti-Lateral side edge EA and the abdomen side edge EB of the gantry 22b intersect is defined as the origin “0” of the three-dimensional orthogonal coordinate system. From the origin of the three-dimensional orthogonal coordinate system, the direction of Anti-Lateral side edge EA is defined as the X-axis direction, the direction of the abdominal side edge EB is defined as the Y-axis direction, and the depth direction of gantry 22b is defined as the Z-axis direction. To do.

  The apparatus main body 23 shown in FIG. 2 is configured based on a computer, and includes a transmission / reception circuit 31, a B-mode processing circuit 32, a cine memory 33, a scan conversion circuit 34, an image composition circuit 35, and a monitor 36.

  Although not shown, the transmission / reception circuit 31 includes a transmission circuit and a reception circuit. The transmission circuit includes a rate pulse generation circuit that generates a rate pulse that determines the repetition period of the ultrasonic pulse to be irradiated, and a delay circuit that determines the convergence time and deflection angle of the ultrasonic beam during ultrasonic transmission. , A transmission delay circuit for determining the timing for driving the N ultrasonic transducers, and a pulser circuit for generating a high-pressure pulse for driving the ultrasonic transducers.

  The rate pulse generation circuit provided in the transmission unit of the transmission / reception circuit 31 supplies the transmission delay circuit with a rate pulse that determines the repetition period of the ultrasonic pulse to be irradiated. The transmission delay circuit is composed of an independent delay circuit that is twice (2N) of the ultrasonic transducer used for ultrasonic transmission, and has a predetermined depth in order to obtain a narrow beam width in ultrasonic transmission. A delay time for converging the sound wave and a delay time for transmitting the ultrasonic wave in a predetermined direction are given to the rate pulse and supplied to the pulser circuit.

  The pulser circuit has the same number of 2N independent drive circuits as the transmission delay circuit, drives the ultrasonic transducer built in the ultrasonic probe 11 and emits ultrasonic waves into the patient. Form.

A part of the ultrasonic wave irradiated into the patient's breast is reflected at an interface or tissue between organs having different acoustic impedances. Further, the reflected wave newly generates an ultrasonic pulse having a center frequency of 2f ₀ due to the non-linear characteristics of the tissue. Therefore, the ultrasonic wave reflected in the tissue and returning to the ultrasonic probe 11 includes an ultrasonic pulse (fundamental wave component) having a center frequency f ₀ at the time of ultrasonic transmission and an ultrasonic pulse (harmonic wave) having a center frequency of 2f _0. Component) is mixed. The reception unit included in the transmission / reception circuit 31 includes a BPF (band pass filter) that acquires a fundamental wave component or a harmonic component of a reception signal, a preamplifier circuit that amplifies a minute signal that is converted into an electric signal by an ultrasonic transducer, An A / D (analog / digital) conversion circuit for digitally converting the received signal of the preamplifier circuit, and a phasing addition circuit including a beamformer circuit and an addition circuit are provided.

  In order to obtain a narrow received beam width, the beamformer circuit sequentially changes the reception directivity of the ultrasonic beam and scans the patient within the convergence delay time for converging the ultrasonic wave from a predetermined depth. A delay time is given to the received signal converted into a digital signal. The adder circuit adds the outputs from the beamformer.

  The B-mode processing circuit 32 generates RAW data for B-mode images (tomographic images) (here, data before scan conversion processing) based on the digital input signal from the transmission / reception circuit 31. Specifically, although not shown, the B-mode processing circuit 32 includes a logarithmic conversion circuit that logarithmically converts the amplitude of the digital input signal from the transmission / reception circuit 31 and relatively emphasizes a weak signal, and the logarithmic conversion circuit. An envelope detection circuit that performs envelope detection on the logarithmically converted digital signal and detects an amplitude envelope is provided. A color Doppler mode processing circuit (not shown) may be provided in parallel with the B mode processing circuit 32.

  The cine memory 33 is configured by a nonvolatile semiconductor memory or the like. The cine memory 33 is a memory that stores, for example, RAW data of live images corresponding to a plurality of frames immediately before the data collection by the three-dimensional ultrasonic diagnostic imaging apparatus 11 is completed (freeze). The cine memory 33 has a capacity for storing a plurality of RAW data, and continuously stores the RAW data until a freeze command is sent from the CPU 41. In general, a so-called loop method is adopted for storage in the cine memory 33. That is, when the storage of the RAW data exceeds the allowable amount of the cine memory 33, the latest RAW data is written into the cine memory 33 by sequentially erasing the old stored RAW data and then writing (overwriting) the new RAW data. Is to be memorized.

  The scan conversion circuit 34 converts the RAW data of the live image output from the B-mode processing circuit 32 into a standard TV signal (TV format signal), and generates a live image.

  The image composition circuit 35 generates display data based on the ultrasonic image output from the scan conversion circuit 34 and the CPU 41 and converts the display data into analog data. The image synthesis circuit 35 synthesizes the image together with character information and scales of various parameters, and outputs the synthesized image as a video signal to the monitor 36.

  The monitor 36 displays an ultrasonic image or the like based on the output from the image synthesis circuit 35.

  In addition, the apparatus main body 23 includes a CPU (central processing unit) 41 as a processor, a comprehensive memory 42, an HD (hard disk) 43, an input device 45, and a communication control device 46.

  The CPU 41 controls the operations of the transmission / reception circuit 31, the signal processing circuit 22, the cine memory 33, the scan conversion circuit 34, the image composition circuit 35, and the monitor 36 in accordance with programs stored in the comprehensive memory 42 and the HD 43 and inputs from the input device 45. To do.

  The comprehensive memory 42 is configured by a nonvolatile semiconductor memory or the like. The comprehensive memory 42 is a storage device that stores various application programs related to IPL (initial program loading), BIOS (basic input / output system), and ultrasonic imaging. Examples of various application programs related to ultrasonic imaging include a live display program and a cine reproduction program. The comprehensive memory 42 also functions as a work memory for the CPU 41.

  The HD 43 is a metal disk coated or vapor-deposited with a magnetic material, and data in the HD 43 can be read and written by an HDD (Hard disk drive) (not shown). The HD 43 stores three-dimensional volume data, and can also store various application programs related to ultrasonic diagnosis as an alternative to the comprehensive memory 42. In addition, based on an OS (operating system) stored in the HD 43, a graphic user interface (GUI) that can use the graphics for displaying information to the user and perform basic operations by the input device 45 is provided. You can also.

  The input device 45 includes, for example, a mouse, a trackball, a mode change switch, a keyboard, and the like. The input device 45 is a device for incorporating various instructions from the operator, a region of interest (ROI) setting instruction, a freeze instruction, various image quality condition setting instructions, and the like into the apparatus main body 23.

  The communication control device 46 performs communication control according to each standard. The communication control device 46 has a function capable of connecting to the network N. Therefore, the three-dimensional ultrasonic image diagnostic apparatus 11 can be connected to the network N outside the three-dimensional ultrasonic image diagnostic apparatus 11 via the communication control device 46.

  FIG. 4 is a block diagram illustrating a hardware configuration of the mammography apparatus 12.

  As shown in FIG. 4, the mammography apparatus 12 mainly includes an imaging system 51 and a DF (digital fluorography) apparatus 52. In addition, although the mammography apparatus 12 shown in FIG. 3 demonstrates the case where the breast of the patient P is imaged in a sitting position, it is not limited to that case. For example, the mammography apparatus 12 may be a case where the breast of the patient P is imaged in the supine position or the like.

  The imaging system 51 includes an X-ray tube 61, an X-ray detection device 62, a compression plate 63 (upper compression plate 63 a and lower compression plate 63 b), a high voltage supply device 64, and a patient support unit 65. The X-ray tube 61 is formed of a plurality of lead feathers on the X-ray emission side and is made of silicon rubber or the like, and a predetermined amount of irradiated X-rays is attenuated to prevent halation. A compensation filter may be provided.

  The X-ray tube 61 is supplied with high voltage power from the high voltage supply circuit 64 and emits X-rays toward the X-ray detection device 62 through the breast of the patient P according to the condition of the high voltage power. To do.

  The X-ray detection apparatus 62 has a flat panel detector (FPD). The X-ray detection device 62 includes a 2D array type X-ray detector as a planar detector that detects X-rays by detecting elements arranged in a 2D shape and converts them into electrical signals, and the 2D array type X-ray detector. The DAS (data acquisition system) collects X-ray detection data detected as an electrical signal by each detection element.

  The compression plate 63 is disposed between the X-ray tube 61 and the X-ray detection device 62, and compresses the breast sandwiched between the upper compression plate 63a and the lower compression plate 63b. The compression plate 63 is formed of a transparent resin, and is supported so as to be able to come into contact with and separate from the X-ray detection device 62 by a driving device (not shown).

  The high voltage supply device 64 supplies high voltage power to the X-ray tube 61 under the control of the DF device 52.

  The patient support unit 65 places the patient P in the sitting position.

  The DF device 52 is configured based on a computer, and can communicate with the network N. In general, the DF device 12 includes an A / D (analog to digital) conversion circuit 71, an image generation / processing circuit 72, an image memory 73, an image composition circuit 74, a monitor 75, a CPU 81, a comprehensive memory 82, an HD 83, and an input device 84. The communication control device 85 and the system control device 86 are configured by hardware. The CPU 81 is interconnected to each hardware component constituting the DF device 52 via a bus as a common signal transmission path. Note that the DF device 52 may include a drive (not shown) for a recording medium.

  The A / D conversion circuit 71 converts the time-series analog signal (video signal) output from the X-ray detection device 62 into a digital signal.

  The image generation / processing circuit 72 performs logarithmic conversion processing (LOG processing) on the digital signal of the projection data output from the A / D conversion circuit 71 under the control of the CPU 81, and performs image processing such as addition processing as necessary. To generate a mammography image (CC (cranial-caudal view) image or MLO (medial-objective-image) image), and store the mammography image in the image memory 73. The mammography image after the image processing by the image generation / processing circuit 72 is output to the image composition circuit 74 and is also stored in a storage device such as the image memory 73.

  The image memory 73 stores a mammography image output from the image generation / processing circuit 72 under the control of the CPU 81.

  Under the control of the CPU 81, the image composition circuit 74 synthesizes the mammography image output from the image generation / processing circuit 72 together with character information, scales, and the like of various parameters, and outputs them as a video signal to the monitor 75.

  The monitor 75 displays a mammography image or the like based on the output from the image composition circuit 74.

  The CPU 81 executes a program stored in the comprehensive memory 82 when a command is input by operating the input device 84 or the like by the operator. Alternatively, the CPU 81 uses a program stored in the HD 83, a program transferred from the network N and received by the communication control device 85 and installed in the HD 83, or a recording medium attached to a recording medium drive (not shown). The program read and installed in the HD 83 is loaded into the comprehensive memory 82 and executed.

  The comprehensive memory 82 is a storage device that stores IPL, BIOS, and data, and is used for temporary storage of the work memory and data of the CPU 81.

  The HD 83 is a metal disk coated or vapor-deposited with a magnetic material, and data in the HD 83 can be read and written by an HDD (not shown). The HD 83 stores a mammography image, and can also store various application programs related to mammography as an alternative to the comprehensive memory 82. Further, based on the OS stored in the HD 83, it is also possible to provide a GUI that allows a basic operation to be performed by the input device 84 by using a lot of graphics for displaying information to the user.

  Examples of the input device 84 include a keyboard and a mouse that can be operated by an operator, and an input signal according to the operation is sent to the CPU 81.

  The communication control device 85 performs communication control according to each standard. The communication control device 85 has a function of being able to connect to the network N, whereby the mammography device 12 can be connected from the communication control device 85 to the network N network.

  The system control device 86 includes a CPU and a memory (not shown). The system control device 86 controls the operation of the high voltage supply device 64 and the like of the imaging system 51 in accordance with an instruction from the CPU 81.

  FIG. 5 is a block diagram illustrating a hardware configuration of the image processing apparatus 13.

  As shown in FIG. 5, the image processing device 13 includes hardware such as a CPU 91, a memory 92, an HD 93, an input device 94, an image composition circuit 95, a monitor 96, and a communication control device 97. The CPU 91 is interconnected to each hardware component constituting the image processing device 13 via a bus as a common signal transmission path. The image processing apparatus 13 may include a recording medium drive (not shown).

  The CPU 91 executes a program stored in the memory 92 when a command is input by operating the input device 94 by an operator. Alternatively, the CPU 91 may be a program stored in the HD 93, a program transferred from the network N, received by the communication control device 97 and installed in the HD 93, or a recording medium mounted on a recording medium drive (not shown). The program read and installed in the HD 93 is loaded into the memory 92 and executed.

  The memory 92 is a storage device that stores IPL, BIOS, and data, and is used for temporary storage of the work memory and data of the CPU 91.

  The HD 93 is a metal disk coated or vapor-deposited with a magnetic material, and data in the HD 93 can be read and written by an HDD (not shown). The HD 93 can also store various application programs as an alternative to the memory 92. Further, based on the OS stored in the HD 93, it is possible to provide a GUI that can use a lot of graphics for displaying information to the user and perform basic operations by the input device 94.

  Examples of the input device 94 include a keyboard and a mouse that can be operated by an operator, and an input signal according to the operation is sent to the CPU 91.

  The image synthesis circuit 95 synthesizes an ultrasonic image and a mammography image together with character information of various parameters, scales, and the like under the control of the CPU 91, and outputs them to the monitor 96 as video signals.

  The monitor 96 displays an ultrasonic image, a mammography image, and the like based on the output from the image synthesis circuit 95.

  The communication control device 97 performs communication control according to each standard. The communication control device 97 has a function of being able to connect to the network N, whereby the image processing device 13 can be connected from the communication control device 97 to the network N network.

  FIG. 6 is a block diagram showing functions of the three-dimensional ultrasonic image diagnostic apparatus 11.

  As illustrated in FIG. 6, the CPU 41 of the three-dimensional ultrasonic diagnostic apparatus 11 illustrated in FIG. 2 executes the program, so that the three-dimensional ultrasonic diagnostic apparatus 11 includes the non-compressed state base marking execution unit 101, the non-compressed state It functions as an inter-base point distance acquisition unit 102, an uncompressed base-point distance recording unit 103, a three-dimensional volume data generation unit 104, and a three-dimensional volume data recording unit 105. The components 101 to 105 of the three-dimensional ultrasound image diagnostic apparatus 11 will be described in terms of software as functions by the CPU 41 executing a program. However, some or all of the components 101 to 105 are hardware. The three-dimensional ultrasonic image diagnostic apparatus 11 may be provided.

  2, the patient P is placed on the top board 22a in the prone position, and the breast of the patient P is inserted into the gantry 22b containing water. Is set, the non-compressed state base marking execution unit 101 uses two contact points of the breast inserted into the gantry 22b and the abdominal side edge EB formed on the top surface of the top plate 22a of the gantry 22b as the base points. It has a function to perform marking on both the breast and the top plate 22a corresponding to. Further, the non-compressed state base point marking execution unit 101 has a function of executing marking on both the breast and the top plate 22a corresponding to the base point with one contact point between the breast and the Anti-Lateral side edge EA as a base point.

  FIG. 7 is a diagram showing the base points α1, α2, and β in the three-dimensional orthogonal coordinate system.

  While the top view of the top plate 22a is shown in the upper stage of FIG. 7, the side view is also shown in the lower stage. In FIG. 7, the base points α1 and α2 as two contact points between the breast inserted into the gantry 22b and the abdomen side edge EB formed on the upper surface of the top plate 22a of the gantry 22b are shown as “●” marks. . Further, in FIG. 7, a base point β as one contact point between the breast and the anti-lateral side edge EA formed on the top surface of the top plate 22a of the gantry 22b is indicated by “▲”.

  FIG. 8 is an enlarged top view showing the relationship between the breast cross section in the XY cross section with Z = 0 and the base points α1, α2, and β.

As shown in FIG. 8, in the XYZ coordinate system, the coordinates of the base points α1, α2, and β are respectively defined as the following formula (1).

  9 and 10 are diagrams for explaining a marking method performed by the non-compressed state base point marking execution unit 101. FIG.

  9A and 9B are diagrams for explaining a marking method when marking is performed automatically, FIG. 9A is a perspective view, and FIG. 9B is a cross-sectional view in the XZ section of Y = 0. . The gantry 22b includes a marker horizontal movement port 100a extending through the marking point of the jig (marker) M through the surface including the abdomen side edge EB of the gantry 22b and extending in the X-axis direction when X = Z = 0, and the gantry 22b. A marker horizontal movement port 100b that penetrates the marking point of the marker M and extends in the X-axis direction at Y = Z = 0 is provided on the surface including the Anti-Lateral side edge EA.

  When marking is performed automatically as shown in FIG. 9, the marker M mechanically moves in the Y-axis direction in the marker horizontal movement port 100a and in the X-axis direction in the marker horizontal movement port 100b. Marking is performed on the base points α1 and α2 with the abdominal side edge EB of the breast by the marker M that moves through the marker horizontal movement opening 100a. In addition, the marker M moving through the marker horizontal moving port 100b is marked at the base point β with the anti-lateral edge EA of the breast. The marker M may be anything as long as it can mark colors on the breast and the top surface of the top plate 22a.

  FIG. 10 is a diagram for explaining a marking method when marking is performed manually, and is a cross-sectional view of a breast in an XY cross section with Z = 0. When marking is performed manually, an operator such as an engineer uses the marker M to mark the breast and the top surface of the top plate 22a. On the top surface of the top plate, a memory for measurement is written in advance in the direction from the origin to the abdomen side edge EB and the Anti-Lateral side edge EA.

6 has a function of acquiring a distance D between base points in a non-compressed state, which is a distance between the base point α1 and the base point α2. The non-compressed state base point distance acquisition unit 102 acquires the base point distance D in the non-compressed state based on the marking on the top plate 22a by the non-compressed state base point marking execution unit 101. The distance D between the base points in the non-compressed state can be expressed as the following formula (2).

  The non-compressed base point distance recording unit 103 has a function of recording the non-compressed base point distance D acquired by the non-compressed base point distance acquisition unit 102 in a storage device such as the HD 43 (shown in FIG. 2). .

  The three-dimensional volume data generation unit 104 controls each hardware component 31 to 36 (shown in FIG. 2) of the three-dimensional ultrasonic image diagnostic apparatus 11 to generate ultrasonic three-dimensional volume data regarding the breast of the patient P. It has a function to generate.

  The three-dimensional volume data recording unit 105 has a function of recording the three-dimensional volume data generated by the three-dimensional volume data generation unit 104 in a storage device such as the HD 43 (shown in FIG. 2).

  The three-dimensional volume data generated by the three-dimensional volume data generation unit 104 is displayed via the monitor 36 (shown in FIG. 2) after image processing such as volume rendering.

  FIG. 11 is a block diagram illustrating functions of the mammography apparatus 12.

  As shown in FIG. 11, when the CPU 81 of the mammography apparatus 12 shown in FIG. 4 executes the program, the mammography apparatus 12 includes a breast compression execution unit 111, a mammography image generation unit 112, a compression state base point distance acquisition unit 113, It functions as a compression state base point distance recording unit 114, a compression state compression plate base point distance acquisition unit 115, a compression state compression plate base point distance recording unit 116, and a mammography image recording unit 117. The components 111 to 117 of the mammography apparatus 12 will be described in terms of software as functions by the CPU 81 executing a program. However, some or all of the components 111 to 117 are provided in the mammography apparatus 12 as hardware. May be.

  The patient P is moved from the imaging location by the three-dimensional ultrasound image diagnostic apparatus 11 to the imaging location by the mammography apparatus 12, and the breast compression execution unit 111 receives a compression plate 63 (shown in FIG. 4) via a drive device (not shown). The upper compression plate 63a and the lower compression plate 63b) are controlled to perform the compression of the breast of the patient P in the sitting position.

  The mammography image generating unit 112 has a function of controlling each hardware component 71 to 75, 86 (shown in FIG. 4) of the mammography apparatus 12 to generate a mammography image regarding the breast of the patient P. Hereinafter, a case where a CC image as a mammography image is generated will be described as an example, but the present invention can also be applied to a case where the mammography image is an MLO image.

  The compression state base point distance acquisition unit 113 has a function of acquiring a compression state base point distance d that is a distance between the base point α1 and the base point α2 marked on the breast.

  FIG. 12 is a perspective view showing the breast in a compressed state.

FIG. 12 shows base points α1, α2, and β marked on the breast of the patient P in the X′Y′Z ′ coordinate system. In FIG. 12, the Y′-axis direction is defined as a straight line passing through the base point α1 and the base point α2. Then, in the X′Y′Z ′ coordinate system, the base points α1 and α2 are defined as in the following formula (3).

The distance d between the base points in the compressed state, which is the distance between the base point α1 and the base point α2, can be expressed as the following equation (4).

  Further, the compression state base point distance recording unit 114 shown in FIG. 11 stores the compression state base point distance d in the compression state acquired by the compression state base point distance acquisition unit 113 in a storage device such as HD83 (shown in FIG. 4). Has the function of recording.

Pressurizing-state compression plate base distance obtaining unit 115 has a function of acquiring a compression plate base distance d _m in compressed state the distance between the base point β marked the breast with the lower compression plate 63 b (shown in FIG. 4) Have

  FIG. 13 is a view showing an X′Z ′ cross-sectional view showing a breast in a compressed state.

FIG. 13 shows the base point β marked on the breast of the patient P in the X′Z ′ coordinate system. In the X′Y′Z ′ coordinate system, the base point β is defined as in the following equation (5).

The compressed state compression plate base distance obtaining unit 115, based on the marking marked on the breast to obtain a compression plate base distance d _m in compressed state. That is, as in the following equation (6), obtain the compression plate base distance d _m of the compression state using a ε of the formula (5).

Also, compressed state compression plate base distance recording section 116 shown in FIG. 11, the compressed state compression plate base distance d _m in compressed state obtained by the compressed state compression plate base distance obtaining unit 115 HD83 (Figure 4 Etc.) and the like.

  The mammography image recording unit 117 has a function of recording the CC image generated by the mammography image generation unit 112 in a storage device such as the HD 43 (shown in FIG. 4).

  Further, the CC image generated by the mammography image generation unit 112 is displayed via the monitor 75 (shown in FIG. 4).

  FIG. 14 is a block diagram illustrating functions of the image processing apparatus 13.

  As illustrated in FIG. 14, the CPU 91 of the image processing device 13 illustrated in FIG. 5 executes the program, so that the image processing device 13 includes a three-dimensional volume data acquisition unit 121, a mammography image acquisition unit 122, an image processing unit 123, Edge maximum value generation unit 124, compression state compression plate base distance acquisition unit 125, X-axis direction compression coefficient generation unit 126, non-compression state base point distance acquisition unit 127, compression state base point distance acquisition unit 128, Y-axis direction compression It functions as a coefficient generation unit 129, a compression state maximum value generation unit 130, a Z-axis direction compression coefficient generation unit 131, a virtual mammography image generation unit 132, and a display control unit 133. Note that the components 121 to 133 of the image processing device 13 are described in terms of software as functions by the CPU 91 executing a program, but some or all of the components 121 to 133 are hardware as the image processing device 13. May be provided.

  The image processing device 13 deforms the ultrasound three-dimensional volume data generated by the three-dimensional ultrasound image diagnostic device 11 to generate a virtual mammography image that is a pseudo compression image, and the mammography image and the virtual mammography image Are also displayed.

  The three-dimensional volume data acquisition unit 121 has a function of acquiring three-dimensional volume data from the three-dimensional ultrasonic image diagnostic apparatus 11 via the network N.

  The mammography image acquisition unit 122 acquires a CC image that is a patient corresponding to the 3D volume data acquired by the 3D volume data acquisition unit 121 and is generated in the same examination from the mammography device 12 via the network N. It has the function to do.

  The image processing unit 123 has a function of sequentially performing binarization processing, edge (contour) detection processing, and edge thinning processing on the CC image acquired by the mammography image acquisition unit 122 to generate an edge image. The outline of the image processing process by the image processing unit 123 is shown in FIG.

The edge maximum value generation unit 124 has a function of generating an edge maximum value X _max in the X-axis direction by applying an edge in the edge image generated by the image processing unit 123 to the XYZ coordinate system in an uncompressed state. As a method for generating the edge maximum value _Xmax , a function provided in a program for processing a simple loop calculation can be used. By the edge maximum value generator 124 Description of a method of generating an edge maximum value _{X max} shown in FIG. 16.

The compression state compression plate base distance acquisition unit 125 is a patient corresponding to the three-dimensional volume data acquired by the three-dimensional volume data acquisition unit 121 and is a compression state between the compression plate base points d generated in the same examination. _m (Expression (6)) is acquired from the mammography apparatus 12 via the network N.

X-axis compression coefficient generation unit 126, the edge maximum value X _max which is generated by the edge maximum value generation unit 124, a compression plate base distance d of the compression condition obtained by the pressed state compression plate base distance obtaining unit 125 _{Based on m,} it has a function of generating a compression coefficient Fx in the X-axis direction using the following equation (7).

  The non-compressed state base-point distance acquisition unit 127 is a patient corresponding to the three-dimensional volume data acquired by the three-dimensional volume data acquisition unit 121 and is generated in the same examination in the non-compressed base point distance D (described above). The function has a function of acquiring the expression (2) from the three-dimensional ultrasonic image diagnostic apparatus 11 via the network N.

  The compression state base point distance acquisition unit 128 is a patient corresponding to the three-dimensional volume data acquired by the three-dimensional volume data acquisition unit 121 and is generated within the same examination in the compression state base point distance d (the above formula ( 4)) is obtained from the mammography apparatus 12 via the network N.

The Y-axis direction compression coefficient generation unit 129 is a compression state base point distance D acquired by the non-compression state base point distance acquisition unit 127 and a compression state base point distance acquired by the compression state base point distance acquisition unit 128. Based on d, it has a function of generating a compression coefficient Fy in the Y-axis direction using the following equation (8). FIG. 17 shows an outline of a method of generating the Y-axis direction compression coefficient by the Y-axis direction compression coefficient generation unit 129.

Based on the CC image acquired by the mammography image acquisition unit 122, the compression state maximum value generation unit 130 is a point η that is the maximum in the X′-axis direction in the X′Y′Z ′ coordinate system according to the following equation (9). And the maximum value d _η of the compressed state, which is the distance between the point η and the Y ′ axis, is generated. FIG. 18 shows an outline of a method for generating the compression state maximum value d _η by the compression state maximum value generation unit 130.

The Z-axis direction compression coefficient generation unit 131 generates a maximum value Z _max in the Z-axis direction from the three-dimensional volume data acquired by the three-dimensional volume data acquisition unit 121, and based on the maximum value Z _max in the Z-axis direction The function of calculating the compression coefficient Fz in the Z-axis direction using the following equation (10) is provided.

  The virtual mammography image generation unit 132 applies the X-axis direction compression coefficient generated by the X-axis direction compression coefficient generation unit 126 to the three-dimensional volume data acquired by the three-dimensional volume data acquisition unit 121 (the above formula (7)). A Y-axis direction compression coefficient generated by the Y-axis direction compression coefficient generation unit 129 (the above equation (8)), and a Z-axis direction compression coefficient generated by the Z-axis direction compression coefficient generation unit 131 (the above equation) (10)) is applied to generate a virtual CC image (virtual mammography image) that is a pseudo compression image.

Specifically, if the data size of the three-dimensional volume data is I × J × K [voxel], the arbitrary point P on the three-dimensional volume data can be expressed as the following equation (11).

Further, when the position of the voxel moved by the compression coefficient is defined as the following expression (12), the position of the moved voxel is expressed by the following expression (13) using the expression (11) and the compression coefficient in the XYZ axis direction. ).

  The virtual mammography image generation unit 132 uses the above equation (13) to transform the 3D volume data acquired by the 3D volume data acquisition unit 121 and generate a virtual CC image that is a pseudo compression image It is possible to support the optimum comparative interpretation of the ultrasonic image and the CC image.

  The display control unit 133 has a function of controlling display of the virtual mammography image generated by the virtual mammography image generation unit 132. In addition, the display control unit 133 has a function of controlling parallel display of a virtual mammography image generated by the virtual mammography image generation unit 132 and a mammography image acquired by the mammography image acquisition unit 122.

  Each of the acquisition units 121, 122, 125, 127, and 128 is configured to acquire desired data via the network N. However, the acquisition units 121, 122, 125, 127, and 128 may be configured to acquire using a recording medium that stores the data. .

  According to the breast examination system 10 of the present embodiment, the mammography image is generated by deforming the breast three-dimensional volume data generated by the three-dimensional ultrasound image diagnostic apparatus 11 to generate a virtual mammography image that is a pseudo compression image. And by displaying the virtual mammography image together, it is possible to realize an appropriate breast examination by comparative interpretation.

FIG. 3 is an idea diagram showing an embodiment of a breast examination system. The block diagram which shows the hardware constitutions of a three-dimensional ultrasonic image diagnostic apparatus. Schematic which shows the structure of a gantry. The block diagram which shows the hardware constitutions of a mammography apparatus. The block diagram which shows the hardware constitutions of an image processing apparatus. The block diagram which shows the function of a three-dimensional ultrasonic image diagnostic apparatus. The figure which shows base point (alpha) 1, (alpha) 2, (beta) in a three-dimensional orthogonal coordinate system. The enlarged top view which shows the relationship between the breast cross section in XY cross section of Z = 0, and base point (alpha) 1, (alpha) 2, (beta). The figure for demonstrating the marking method. The figure for demonstrating the marking method. The block diagram which shows the function of a mammography apparatus. The perspective view which shows the breast of the state compressed. The figure which shows X'Z 'sectional drawing which shows the breast of the state compressed. The block diagram which shows the function of an image processing apparatus. The figure which shows the outline | summary of an image processing process. The figure which shows the outline | summary of the production | generation method of edge maximum value. The figure which shows the outline | summary of the production | generation method of a Y-axis direction compression coefficient. The figure which shows the outline | summary of the production | generation method of a compression state maximum value.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Breast examination system 11 Three-dimensional ultrasound image diagnostic apparatus 12 Mammography apparatus 13 Image processing apparatus 101 Non-compressed state base point marking execution unit 102 Non-compressed state base point distance acquisition unit 103 Non-compressed state base point distance recording unit 104 Three-dimensional volume data Generation unit 105 Three-dimensional volume data recording unit 111 Breast compression execution unit 112 Mammography image generation unit 113 Compression state base point distance acquisition unit 114 Compression state base point distance recording unit 115 Compression state compression plate base point distance acquisition unit 116 Compression state compression plate Reference point distance recording unit 117 Mammography image recording unit 121 Three-dimensional volume data acquisition unit 122 Mammography image acquisition unit 123 Image processing unit 124 Maximum edge value generation unit 125 Compression state compression plate base point distance acquisition unit 126 X-axis direction compression coefficient generation unit 127 Uncompressed state Point distance acquiring part 128 pressed state base distance obtaining unit 129 Y-axis direction compression coefficient generator 130 compressed state maximum value generation unit 131 Z-axis compression coefficient generator 132 virtual mammographic image generation unit 133 display control unit

Claims (2)

In a breast examination system that generates and displays mammography images and ultrasound images,
A virtual mammography image generation unit that generates a virtual mammography image that is a pseudo-compressed image by transforming ultrasonic three-dimensional volume data;
A display control unit for controlling display of the mammography image and the virtual mammography image;
A breast examination system characterized by comprising: The apparatus further includes a compression coefficient generation unit that generates a compression coefficient converted into a three-dimensional orthogonal coordinate system in the generation environment of the three-dimensional volume data, and the virtual mammography image generation unit uses the compression coefficient as the three-dimensional volume data. The breast examination system according to claim 1, wherein the breast examination system is configured to generate the virtual mammography image by applying to a computer.

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