JP2013085622A - Medical image diagnostic apparatus, medical image display device, and control program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To preponderantly display image data collected from a disease region.SOLUTION: This medical image diagnostic apparatus 100 is constituted so as to perform the formation and display of the image data in a plurality of different image cross sections on the basis of the volume data collected from a subject and configured to include an image data forming part 6 for forming the image data in the image cross sections set with respect to the volume data, a disease region detection part 7 for detecting the disease region on the basis of the voxel value of the volume data, a concerned region setting part 8 for setting a concerned region having a predetermined shape to the disease region of the volume data, a display data forming part 9 for forming display data for preponderantly displaying the image data in the image cross section crossing the concerned region, and a display part 10 for displaying the display data.

Description

  Embodiments described herein relate generally to a medical image diagnostic apparatus, a medical image display apparatus, and a control program capable of observing image data collected from a diseased area of a subject with priority.

  Medical image diagnosis using an X-ray diagnostic apparatus, an MRI apparatus, an X-ray CT apparatus, a nuclear medicine imaging apparatus, etc. has made rapid progress along with the development of computer technology and has become indispensable in today's medical care. Yes.

  The above-mentioned X-ray diagnostic apparatus and X-ray CT apparatus are intended for so-called morphological diagnosis in which an outline of an organ, a tumor, or the like is drawn, whereas a nuclear medicine imaging apparatus is selected as a living tissue. Γ-rays emitted from a radioactive isotope or a labeled compound that is taken in automatically are measured from outside the body, and the dose distribution is imaged to enable functional diagnosis on the subject.

  As the above-mentioned nuclear medicine imaging apparatus, a gamma camera, a single photon emission CT apparatus (SPECT (Single Photon Emission Computed Tomography) apparatus), a positron emission CT apparatus (PET (Positron Emission Computed Tomography) apparatus), etc. are used in clinical settings. For example, a PET device administers a radioisotope labeled with a nuclide that emits a positron (positron) to a subject, and arranges it around the subject when the positron combines with the electron and disappears. Image data is generated by reconstructing a pair of gamma ray information detected by the ring-shaped detector.

  Further, in recent years, a morphological image diagnostic apparatus such as an X-ray CT apparatus and an MRI apparatus capable of collecting morphological image data and a functional image diagnostic apparatus such as a PET apparatus and a SPECT apparatus capable of collecting functional image data are integrated. A new medical image diagnostic apparatus has been newly developed, and by using such a medical image diagnostic apparatus, it has become possible to efficiently collect morphological image data and functional image data in the whole body region of the subject.

  However, due to the practical application of such a medical image diagnostic apparatus, an extremely large amount of image data is collected in a single examination of a subject, and with the development of high resolution technology in the generation of image data, the interpretation of these image data is performed. The burden on doctors in charge of medical care is increasing. In order to improve such problems, a diagnosis support system capable of automatically detecting a diseased part such as a tumor indicated in image data and reducing the time required for diagnosis (image interpretation) is provided. Proposed.

JP 2010-29481 A

  Significant improvement in diagnostic efficiency is expected by the above-described method of performing image diagnosis on the subject based on automatically detected image data of a diseased part such as a tumor. However, since it is impossible with current image processing technology to reliably detect diseased parts having various sizes and shapes, there is a problem that the risk of overlooking the diseased part must always be considered. It was.

  The present disclosure has been made in view of the above-described problems, and an object thereof is to use the image data or the generation of the image data when making a diagnosis using a lot of image data collected from a subject. Medical image diagnostic apparatus and medical image display capable of shortening the time required for interpretation and reducing the risk of oversight with respect to the diseased region by intensively displaying the diseased region automatically detected based on the received image information To provide an apparatus and a control program.

  In order to solve the above-described problem, the medical image diagnostic apparatus according to the present disclosure is a medical image diagnostic apparatus that generates and displays image data in a plurality of different image cross sections based on volume data collected from a subject. Image data generating means for generating image data in the image slice set for the disease, disease area detecting means for detecting a disease area based on a voxel value of the volume data, and a predetermined shape for the disease area of the volume data A region of interest setting means for setting a region of interest, display data generating means for generating display data for intensively displaying the image data generated in the image section intersecting with the region of interest, and displaying the display data And a display means for performing the operation.

1 is a block diagram showing the overall configuration of a medical image diagnostic apparatus according to a first embodiment. The block diagram which shows the specific structure of the morphological image information collection part with which the medical image diagnostic apparatus of 1st Embodiment is provided. The block diagram which shows the specific structure of the functional image information collection part with which the medical image diagnostic apparatus of 1st Embodiment is provided. The figure for demonstrating the detector module with which the functional image information collection part of 1st Embodiment is provided. The figure for demonstrating the specific example of the image cross section formed by the image cross-section formation part with which the medical image diagnostic apparatus of 1st Embodiment is provided. The block diagram which shows the specific structure of the disease area | region detection part with which the medical image diagnostic apparatus of 1st Embodiment is provided. The figure which shows the specific example of the profile data produced | generated in the disease area | region detection part of 1st Embodiment. The block diagram which shows the specific structure of the display data generation part with which the medical image diagnostic apparatus of 1st Embodiment is provided. The figure which shows the specific example of the display data produced | generated in the display data production | generation part of 1st Embodiment. The figure for demonstrating the attention data collection area | region set by the attention data area | region setting part with which the medical image diagnostic apparatus of 1st Embodiment is provided. The figure for demonstrating the X-ray CT mount part and PET mount part with which the medical image diagnostic apparatus of 1st Embodiment is provided. 6 is a flowchart illustrating a display data generation / display procedure according to the first embodiment. The block diagram which shows the whole structure of the medical image display apparatus in 2nd Embodiment.

  Hereinafter, embodiments of the present disclosure will be described with reference to the drawings.

(First embodiment)
In the medical image diagnostic apparatus according to the present embodiment, first, three-dimensional morphological image information (morphological volume data) and functional image information (functional volume data) are collected by X-ray CT imaging and PET imaging of a subject. A plurality of image slices perpendicular to the body axis direction are formed with respect to the morphological volume data and functional volume data, and morphological image data and functional image data in each image slice are generated. Next, a disease candidate region is detected based on the SUV value of the SUV data obtained by processing the voxel value of the functional volume data, and the disease region is detected based on the profile data of the SUV data in this disease candidate region. Then, image data collected in an image cross section intersecting with a region of interest having a predetermined shape set so as to surround the disease region is displayed with priority. For example, a cine display mode is selected in which the morphological image data and functional image data generated in the image cross section corresponding to the display cross section are displayed in time series while the display cross section indicated by the slice marker is sequentially moved in the body axis direction. The display speed of the image data collected in the image cross section intersecting with the above-mentioned region of interest (the number of image data displayed in the unit time) is the display speed of the image data collected in the other image cross section. The display speed of the morphological image data and the functional image data is controlled so as to be slower.

  In the following embodiments, a medical image diagnostic apparatus having a morphological image information collecting unit for collecting morphological volume data by X-ray CT imaging and a functional image information collecting unit for collecting functional volume data by PET imaging will be described. For example, the morphological image information collection unit may collect morphological volume data by MRI imaging, and the functional image information collection unit collects functional volume data by SPECT imaging. May be.

  In addition, a case where two-dimensional morphological image data and functional image data in a plurality of image cross sections (axial cross sections) perpendicular to the body axis direction of the subject are generated based on the volume data described above will be described. It may be an image cross section (coronal cross section or sagittal cross section) or morphological image data and functional image data in an arbitrary image cross section.

(Device configuration)
The configuration of the medical image diagnostic apparatus according to the present embodiment will be described with reference to FIGS. FIG. 1 is a block diagram showing the overall configuration of the medical image diagnostic apparatus according to the present embodiment. FIGS. 2 and 3 are diagrams of a morphological image information collecting unit and a functional image information collecting unit provided in the medical image diagnostic apparatus. It is a block diagram which shows a specific structure. 6 and 8 are block diagrams showing specific configurations of a disease region detection unit and a display data generation unit provided in the medical image diagnostic apparatus.

  The medical image diagnostic apparatus 100 according to the present embodiment shown in FIG. 1 generates projection data by detecting X-rays emitted from the X-ray generation unit 21 of the rotating gantry unit and transmitted through the subject 150 by the projection data generation unit 22. A morphological image information collecting unit (X-ray CT imaging unit) 2 that generates morphological volume data based on the projection data, and a pair of γ rays emitted from the body of the subject 150 to which the radioisotope is administered. A functional image information collection unit (PET imaging unit) 3 that generates a projection volume by detecting a detection direction and a detection position and generates functional volume data based on the projection data, a morphological image information collection unit 2 and a functional image information The volume data storage unit 4 that stores the volume data generated in the collection unit 3, and the body of the subject 150 with respect to the above-described form volume data and functional volume data An image slice forming unit 5 for forming a plurality of image slices (axial slices) perpendicular to the direction (z-axis direction in FIG. 1), and the form volume data and functional volume data read from the volume data storage unit 4 in the image slices A plurality of morphological image data and functional image data perpendicular to the body axis direction of the subject 150 are generated based on the voxels, and further, MIP (maximum in the front direction and side surface direction of the subject 150 is based on the functional volume data described above. An image data generation unit 6 for generating image data is provided.

  The medical image diagnostic apparatus 100 also includes a disease region detection unit 7 that detects a disease region of the subject 150 based on the functional volume data supplied from the volume data storage unit 4, and a region of interest of a predetermined size surrounding the disease region. The region-of-interest setting unit 8 that is set for the functional volume data and the morphological volume data described above, and the morphological image data, functional image data, and MIP image data generated by the image data generating unit 6 include thumbnail data and disease of functional image data. A display data generation unit 9 that generates display data by adding an SUV value calculated later in the region detection unit 7 and a half width FWHM (full width at half maximum) of profile data and the like, and a display data generation unit 9 Set by the display unit 10 for displaying the display data described above and the region of interest setting unit 8 Based on the position information of the heart region and the position information of the image slice formed in the image slice forming unit 5, the region in which morphological image data and functional image data effective for diagnosis of the disease region are collected is set as the attention data collection region The attention data area setting unit 11 that performs the display, and controls the display speed of the morphological image data and functional image data collected in the attention data collection area and the display speed of the morphological image data and functional image data collected in the area other than the attention data collection area. A PET equipped with a speed control unit 12, a top plate 13 placed on a couch (not shown) on which a subject 150 is placed, an X-ray CT gantry unit having a morphological image information collection unit 2, and a functional image information collection unit 3 A moving mechanism 1 for moving the gantry (not shown) in the direction of the body axis to place the region to be examined in each imaging field 4 and an input unit 15 for inputting subject information, setting imaging conditions and volume data collection conditions, setting image data generation conditions and display data generation conditions, setting display data display conditions, inputting various instruction signals, and the like. A system control unit 16 that controls the above-described units of the medical image diagnostic apparatus 100 is provided.

  Next, the configuration and function of each of the units included in the medical image diagnostic apparatus 100 will be described in more detail.

  The morphological image information collection unit 2 shown in FIG. 1 includes an X-ray generation unit 21, a projection data generation unit 22, a rotary gantry unit 23, a fixed gantry unit 24, and a morphological volume data generation unit 25, as shown in FIG. The X-ray generation unit 21 includes an X-ray tube 211 that irradiates the subject 150 with X-rays, a high voltage generator 212 that generates a high voltage applied between the anode and the cathode of the X-ray tube 211, An X-ray restrictor 213 that sets an irradiation range of X-rays radiated from the X-ray tube 211 and a slip ring 214 that supplies the above-described high voltage to the X-ray tube 211 of the rotary mount unit 23 are provided. The X-ray tube 211 is a vacuum tube that generates X-rays, and emits X-rays by colliding electrons accelerated by a high voltage supplied from the high-voltage generator 212 with a tungsten target. On the other hand, the X-ray restrictor 213 is provided between the X-ray tube 211 and the subject 150 and has a function of narrowing X-rays emitted from the X-ray tube 211 to a predetermined imaging region and X-ray irradiation to the subject 150. It has a function to set the intensity distribution. For example, the X-ray beam radiated from the X-ray tube 211 is formed into a cone beam-shaped or fan beam-shaped X-ray beam corresponding to the imaging region.

  Next, the projection data generation unit 22 detects an X-ray that has passed through the subject 150, and performs current / voltage conversion or A for the detection signals of a plurality of channels output from the X-ray detector 221. A data acquisition unit (hereinafter referred to as a DAS (Data Acquisition System) unit) 222 that performs signal processing such as / D conversion, and parallel / serial conversion, electrical / optical / electrical conversion, and output from the DAS unit 222 A data transmission circuit 223 that performs serial / parallel conversion is provided.

  The X-ray detector 221 of the projection data generation unit 22 includes, for example, a plurality of X-ray detection elements (not shown) that are two-dimensionally arranged. Each of the X-ray detection elements includes a scintillator that converts X-rays into light. It is composed of a photodiode that converts light into an electrical signal. These X-ray detection elements are attached to the rotating gantry 23 along an arc centered on the focal point of the X-ray tube 211.

  On the other hand, the DAS unit 222 performs current / voltage conversion, A / D conversion, and the like on the detection signal of the X-ray detector 221. The data transmission circuit 223 includes a parallel / serial converter, an electrical / optical / electrical converter, and a serial / parallel converter (not shown), and the detection signal output from the DAS unit 222 is attached to the rotary mount 23. Is converted into time-series projection data of one channel in the parallel / serial converter, and is supplied to the serial / parallel converter attached to the fixed base 24 by optical communication using the electrical / optical / electrical converter. The

  Next, the projection data for one channel is converted into projection data for a plurality of channels by a serial / parallel converter and stored in a projection data storage unit (not shown) included in the configuration volume data generation unit 25.

  Note that the above-described data transmission method allows the signal transmission between the projection data generation unit 22 provided on the rotary mount unit 23 and the configuration volume data generation unit 25 provided outside the fixed mount unit 24. For example, a device such as the slip ring described above may be used. In this case, the X-ray tube 211 and the X-ray diaphragm 213 of the X-ray generator 21 and the X-ray detector 221 and the DAS unit 222 of the projection data generator 22 rotate opposite to each other with the subject 150 interposed therebetween. Mounted on the gantry 23.

  The morphological volume data generation unit 25 includes a projection data storage unit, a reconstruction processing unit, and a data processing unit (not shown). The projection data generated by the projection data generation unit 22 is stored in the projection data storage unit 22 of the rotary gantry unit 23. The rotation angle information and the like are stored as incidental information. On the other hand, the reconstruction processing unit reconstructs the projection data read from the projection data storage unit to generate morphological volume data, and the data processing unit performs data such as interpolation processing on the obtained morphological volume data. Perform processing. Then, the form volume data after the data processing is stored in the form volume data storage unit 41 of the volume data storage unit 4 shown in FIG.

  Next, as shown in FIG. 3, the functional image information collection unit 3 in FIG. 1 is arranged concentrically around the subject 150 and is emitted from the body of the subject 150 to which the radioisotope is administered. Based on a detector module 31 for detecting a pair of gamma rays, discrimination between the detected gamma rays and noise, measurement of a gamma ray detection time and detection position, detection position of a pair of gamma rays measured simultaneously, and the like A detection data processing unit 32 that performs measurement of the detection direction and further generates projection data by accumulating the count value of γ rays in a predetermined period in correspondence with the γ-ray detection position and the γ-ray detection direction. A functional volume data generation unit 33 for generating functional volume data by reconstructing the projection data.

  A plurality of detector modules 31 (31-1 to 31-Nm) are concentrically around the subject 150 placed in the imaging field of the functional image information collection unit 3 while being placed on the top board 13. Γ rays emitted from the subject 150 are once converted into visible light by these detector modules 31 and then converted into electrical signals (detection signals).

  FIG. 4 shows a specific configuration of the detector module 31. Each of the detector modules 31-1 to 31 -Nm detects γ-rays radiated from the subject 150 and converts them into visible light. A strip-shaped scintillator 311 for conversion, a photomultiplier tube 312 for converting visible light converted by the scintillator 311 into an electric signal and amplifying the weak electric signal thus converted, and visible light output from the scintillator 311 for photoelectrons A light guide 313 that transmits to the multiplier tube 312 is provided.

The scintillator 311 is made of a material such as bismuth germanide (BGO: (Bi ₄ Ge ₃ O ₁₂ )), thallium activated sodium iodide (NaI (Tl)), barium fluoride (BaF ₂ ), etc. The detector module 31 of the image information collecting unit 3 is preferably bismuth germanide having a high γ-ray photoelectric absorption per unit volume or barium fluoride having a fast response speed.

For example, the photomultiplier tube 312 amplifies several hundreds of photons into 10 ⁷ to 10 ¹⁰ electrons, collects the electrons at an anode as an output stage, and converts them into an electrical signal, not shown. A photocathode and an electron multiplier are provided. For the photocathode, a multi-alkali material whose wavelength characteristic is substantially equal to the emission wavelength of the scintillator 311 or a bi-alkali material activated with oxygen or cesium is used, and the number of generated photoelectrons with respect to the number of incident photons is usually 20% to 30%. It is. On the other hand, the electron multiplier is composed of multi-stage electrodes arranged along an electron propagation path and an anode for collecting amplified electrons based on the secondary electron emission phenomenon. The tube voltage for amplification factor per stage in the case of 200V to 300V is about 5-fold, 10-stage approximately electrode is provided in order to obtain a ¹⁰⁷ amplification factor of the above.

  The light guide 313 is for optically coupling the scintillator 311 and the photomultiplier tube 312, and is light transmissive in order to efficiently transmit visible light output from the scintillator 311 to the photomultiplier tube 312. Excellent plastic material is used.

  Returning to FIG. 3, the detection data processing unit 32 of the functional image information collection unit 3 includes Nm-channel data processing units 321-1 to 321 connected to the detector modules 31-1 to 31-Nm described above. -Nm, a detection direction measurement unit 322 that measures the detection direction of γ-rays based on the detection position information of γ-rays output from these data processing units 321, and γ-ray detection of the count value of the detection signal in a predetermined period A projection data generation unit 323 that generates projection data in the PET imaging mode by sequentially performing cumulative addition corresponding to the position and the γ-ray detection direction is provided.

  Here, it is assumed that a pair of gamma rays emitted from the radioisotope S administered to the subject 150 is detected by the detector modules 31-a and 31-b, and the detector module 31- Only the data processing units 321-a and 321-b connected to a and 31-b are shown.

  The data processing units 321-a and 321-b of the detection data processing unit 32 add and synthesize the detection signals of a plurality of channels supplied from the photomultiplier tubes 312 of the detector modules 31-a and 31-b. 331, a signal discriminating unit 332 for discriminating a detection signal and noise caused by γ-rays based on the respective peak values using the detection signal synthesized in the signal synthesizing unit 331, and output from the signal synthesizing unit 331 The waveform shaping unit 333 that shapes the detection signal after synthesis into a rectangular wave, and the front edge of the rectangular wave that is supplied from the waveform shaping unit 333 with the detection time of the γ-ray corresponding to the detection signal discriminated by the signal discrimination unit 332 The detection time measuring unit 334 that measures based on the detection time, and the detection position of the γ-ray corresponding to the detection signal discriminated by the signal discriminating unit 332 are detected by the detector module 3. Based from -a and 31-b of the photomultiplier tube 312 to the detection signals of a plurality of channels supplied and a detection position measuring unit 335 that measures. The specific configuration and function of each unit constituting the data processing unit 321 are described in Japanese Patent Application Laid-Open No. 2007-107995 and the like, and thus detailed description thereof is omitted.

  Next, the detection direction measurement unit 322 of the detection data processing unit 32 measures the detection time and detection position of γ rays supplied from the detection time measurement unit 334 provided in each of the data processing units 321-1 to 321-Nm. Based on the information on the detection position of the γ rays supplied from the unit 335, the detection direction of the γ rays emitted from the body of the subject 150 is measured.

  On the other hand, the projection data generation unit 323 includes a storage circuit (not shown) having a cumulative calculation function, and associates the count value of the detection signal supplied from the detection direction measurement unit 322 with the above-described detection position and detection direction of the γ-ray. Save in the storage circuit. For example, every time the detection of the γ-rays by the detector module 31-a and the detector module 31-b is performed in a predetermined period, the count value of the detection signal is the value of the memory circuit corresponding to the detection position and the detection direction. Cumulative addition is performed at the address.

  Further, even when a pair of γ-rays is detected in another detector module 31 different from the detector module 31-a and the detector module 31-b, the γ-ray detection position and detection direction are the same as described above. Measurement is performed by the method, and the count value of the detection signal is cumulatively added at the address of the storage circuit corresponding to the detection position and detection direction of the γ-ray. In other words, the count value of γ-rays sequentially detected within a predetermined period is cumulatively added at the address of the storage circuit corresponding to the detection position and detection direction to generate projection data.

  The functional volume data generation unit 33 includes a projection data storage unit, a reconstruction processing unit, and a data processing unit (not shown). The projection data storage unit includes projection data generated by the projection data generation unit 323 of the detection data processing unit 32. Are stored as incidental information such as the detection position and the detection direction. On the other hand, the reconstruction processing unit reconstructs the projection data read from the projection data storage unit to generate functional volume data, and the data processing unit performs data such as interpolation processing on the obtained functional volume data. Perform processing. Then, the functional volume data after the data processing is stored in the functional volume data storage unit 42 of the volume data storage unit 4 shown in FIG.

  Next, the image slice forming unit 5 in FIG. 1 forms a plurality of image slices based on the image data generation conditions set in the input unit 15. FIG. 5 shows N image cross sections (axial cross sections) S1 to SN perpendicular to the body axis direction (z-axis direction) of the subject 150. The image cross section forming unit 5 is connected to the system from the input unit 15. Based on the selection information of the image cross section (axial cross section) included in the image data generation conditions supplied via the control unit 16, the position coordinate Z1 of the axial cross section S1, the number N of image cross sections, the image cross section interval d, and the like. Image cross sections (axial cross sections S1 to SN) with respect to the specimen 150 are formed.

  In the present embodiment, when the above-described axial sections S1 to SN are set for each of the morphological volume data and the functional volume data collected from the subject 150, N morphological image data and functional image data are generated. As described above, the image section is not limited to the axial section. For example, a plurality of coronal sections (coronal sections) or sagittal sections (sagittal sections) parallel to the body axis direction are image sections. You may choose as.

  Next, the image data generation unit 6 includes a morphological image data generation unit 61, a functional image data generation unit 62, and a MIP image data generation unit 63 as shown in FIG. Then, the morphological image data generation unit 61 sets the axial slices S1 to SN supplied from the image slice forming unit 5 to the morphological volume data read from the morphological volume data storage unit 41 of the volume data storage unit 4, and sets these axial data N morphological image data are generated by extracting voxels of morphological volume data existing in the cross section. Similarly, the functional image data generation unit 62 generates N functional image data by setting the axial sections S1 to SN in the functional volume data read from the functional volume data storage unit 42.

  On the other hand, the MIP image data generation unit 63 perpendicularizes the functional volume data read from the functional volume data storage unit 42 described above to the front direction (y direction in FIG. 5) and the side direction (x direction in FIG. 5) of the subject 150. Projecting a maximum value onto a simple projection plane (that is, selecting a voxel having the maximum voxel value from a plurality of voxels arranged in each of a plurality of projection axes perpendicular to the projection plane and projecting it onto the projection plane) MIP image data in the front direction and the side direction is generated.

  Next, a specific configuration and function of the disease region detection unit 7 will be described with reference to the block diagram of FIG. As shown in FIG. 6, the disease region detection unit 7 includes a disease candidate region detection unit 71 having an SUV data generation unit 711, a filtering processing unit 712, and an SUV comparison unit 713, a region center detection unit 721, and a profile data generation unit. 722 and a disease region determination unit 72 having a FWHM comparison unit 723.

  The SUV data generation unit 711 of the disease candidate region detection unit 71 administers the weight / radioisotope of the subject 150 to the voxel value (radioactivity concentration of the radioisotope) of the functional volume data read from the functional volume data storage unit 42. By multiplying the amount, three-dimensional SUV data having an index value SUV (standardized uptake value) that can be quantitatively evaluated without being influenced by the above-described body weight or dose is generated.

  The filtering processing unit 712 performs filtering processing for noise removal and smoothing on the SUV data output from the SUV data generation unit 711 as necessary, and the SUV comparison unit 713 performs filtering processing on the SUV data after filtering processing. By comparing the voxel value with a predetermined threshold value α (for example, α = 4.0), one or a plurality of disease candidate regions in which many radioisotopes are accumulated are detected.

  On the other hand, the region center detection unit 721 of the disease region determination unit 72 detects the center of the disease candidate region by calculating the center of gravity or the center of each disease candidate region detected by the SUV comparison unit 713. Next, the profile data generation unit 722 uses the center of the disease candidate region detected by the region center detection unit 721 as the origin, and is, for example, an orthogonal coordinate system XY-parallel to the orthogonal coordinate system xyz in FIG. Z is set for the SUV data after the filtering process. Then, profile data in the X-axis direction to the Z-axis direction is generated based on the voxel values of the SUV data existing on each axis.

  FIG. 7 shows the profile data Pfx in the X-axis direction generated by the above-described profile data generation unit 722. The horizontal axis represents the coordinates in the X-axis direction including the center Xo of the disease candidate region, and the vertical axis represents Voxel values of SUV data existing on the X axis are shown. The range of the profile data Pfx having a value larger than the threshold value α indicates the width of the disease candidate region detected by the SUV comparison unit 713. Similarly, profile data Pfy in the Y-axis direction and profile data Pfz in the Z-axis direction are generated by the profile data generation unit 722.

  Next, the FWHM comparison unit 723 detects, for example, the maximum value Dmx of the profile data Pfx (see FIG. 7) generated in the profile data generation unit 722 and has a value of Dhx = Dmx / 2. The half width FWHMx (full width at half maximum) of the profile data Pfx is measured. Next, the obtained half width FWHMx is compared with a predetermined threshold value (lower limit value) β1 (for example, β1 = 5 mm) and a threshold value (upper limit value) β2 (for example, β2 = 20 mm). Similarly, the half-value width FWHMy of the profile data Pfy in the Y-axis direction and the half-value width FWHMz of the profile data Pfz in the Z-axis direction are compared with the above-described threshold value β1 and threshold value β2.

  When any of the half-value width FWHMx to the half-value width FWHMz is greater than the threshold value β1 and smaller than the threshold value β2, the disease candidate region is determined as a disease region having a true disease. On the other hand, when FWHM is smaller than the threshold value β1, the disease candidate region is regarded as a noise region, and when FWHM is larger than the threshold value β2, the disease candidate region is regarded as a part of a normal organ having a continuous SUV distribution.

  In addition, when any of the half-value width FWHMx to the half-value width FWHMz is smaller than the threshold value β1 or larger than the threshold value β2, the orthogonal coordinate system XYZ is set to the center of the disease candidate region (Xo, Yo, Zo). A new Cartesian coordinate system is formed by rotating it around the predetermined direction in the predetermined direction, and the half width FWHM (FWHMx to FWHMz) of the profile data generated in the new Cartesian coordinate system is compared with the threshold β1 and the threshold β2. To do. Then, the update of the Cartesian coordinate system and the comparison of the half-value width FWHM, the threshold value β1, and the threshold value β2 in the updated Cartesian coordinate system are repeated a predetermined number of times until both of the half-value widths FWHM satisfy β1 <FWHM <β2. In any orthogonal coordinate system, if any of the half-value widths FWHM satisfies FWHM <β1 or FWHM> β2, the disease candidate region is determined as a non-disease region.

  Here, the method of repeating the update of the orthogonal coordinate system until any of the half-value width FWHMx to half-value width FWHMz of the profile data is larger than the threshold value β1 and smaller than the threshold value β2 has been described. It is not limited to. For example, the profile data generation unit 722 of the disease region determination unit 72 illustrated in FIG. 6 has a plurality of directions (for example, six directions to approximately) formed radially around the center of gravity of the disease candidate region detected by the region center detection unit 721. Profile data is generated in (12 directions), and the FWHM comparison unit 723 compares the half-value width of these profile data with the threshold value β1 and the threshold value β2. If the number of profile data having a half width greater than the threshold value β1 and smaller than β2 is greater than the preset Nx, the disease candidate region is determined as a disease region, and if smaller than Nx, it is determined as a non-disease region. May be.

  Next, the region-of-interest setting unit 8 illustrated in FIG. 1 receives the disease region determination result supplied from the disease region determination unit 72. When there is a disease region having a true disease in one or a plurality of disease candidate regions detected by the SUV comparison unit 713, the determination result is supplied from the input unit 15 via the system control unit 16. The morphological volume stored in the morphological volume data storage unit 41 based on the region-of-interest condition (for example, the shape and size of the region of interest) and the center position information of the disease candidate region supplied from the disease region determination unit 72 A three-dimensional region of interest having a predetermined shape and size is set for the diseased region of the functional volume data stored in the data and functional volume data storage unit 42.

  In this case, for example, the region of interest is set so that the center (hot spot) of the disease candidate region determined as the disease region matches the center of the region of interest having a predetermined shape and size. If the position or size of the region of interest is not suitable for the diseased region, the region of interest is manually updated using the input device of the input unit 15.

  Next, the specific configuration and function of the display data generation unit 9 shown in FIG. 1 will be described with reference to the block diagram of FIG. The display data generation unit 9 includes a data storage unit 91, a thumbnail data generation unit 92, a slice marker generation unit 93, and a data synthesis unit 94.

  The data storage unit 91 is generated in the functional image data storage unit 911 and the morphological image data generation unit 61 that store the functional image data of the image slices S1 to SN generated in the functional image data generation unit 62 of the image data generation unit 6. Further, a morphological image data storage unit 912 that stores morphological image data in the image section, and a MIP image data storage unit 913 that stores MIP image data in the front direction and the side direction of the subject 150 generated by the MIP image data generation unit 63. The FWHM storage unit 914 that stores the full width at half maximum FWHM of the profile data measured by the FWHM comparison unit 723 of the disease region determination unit 72, and the functional volume calculated by the SUV data generation unit 711 of the disease candidate region detection unit 71 SUV storage unit 91 for storing SUV values of data The has.

  The thumbnail data generation unit 92 receives the position information of the slice marker supplied from the slice marker generation unit 93 and the functional image data in the image slices S1 to SN read from the functional image data storage unit 911, and uses the slice marker as a reference. Thumbnail data is generated by reducing the plurality of functional image data in the predetermined range. On the other hand, the slice marker generation unit 93 displays a slice marker corresponding to the display section set by the input unit 15 in the fixed display mode, or a display speed control signal supplied from the display speed control unit 12 described later in the cine display mode. A slice marker having a moving speed corresponding to the speed is generated.

  Then, the data synthesis unit 94 receives the position information of the slice marker supplied from the slice marker generation unit 93, and the functional image data and the morphological image data in the image cross section that matches the slice marker are stored in the functional image of the data storage unit 91. Data are read from the data storage unit 911 and the morphological image data storage unit 912 at a predetermined reading speed. Next, the functional image data and morphological image data described above, the MIP image data in the front direction and the side direction of the subject 150 read from the MIP image data storage unit 913, and the thumbnail data generated by the thumbnail data generation unit 92 are combined. Further, display data is generated by adding the FWHM and SUV values of the region of interest intersecting with the slice marker read from the FWHM storage unit 914 and the SUV storage unit 915 to the above-described image data.

  In addition, the morphological image data and the functional image data collected in advance in the image slices S1 to SN or a part of the image slices are displayed in time series by sequentially moving the display slices indicated by the slice markers in the body axis direction. In the so-called cine display mode, the data synthesizing unit 94 performs functional image data and morphological images for the data storage unit 91 at a reading speed corresponding to a display speed of a display speed control signal supplied from the display speed control unit 12 described later. By reading the data, the display speed of the morphological image data and functional image data collected in the image cross section intersecting with the region of interest having the disease area is the same as that of the morphological image data and functional image data collected in the other image cross sections. Set slower than the display speed. Then, by controlling the display speed as described above, a medical worker who operates the medical image diagnostic apparatus 100 (hereinafter referred to as an operator) can obtain morphological image data and functional image data obtained from a disease region and its peripheral region. Can be read accurately.

  Next, a specific example of display data generated by the display data generation unit 9 will be described with reference to FIG. FIG. 9A shows MIP image data (a-1) generated in the front direction of the subject 150 and MIP image data (a-2) generated in the side direction, and these MIP image data include The slice marker SM that can be moved in the body axis direction generated by the slice marker generator 93 is superimposed. On the other hand, FIG. 9B is thumbnail data of functional image data generated in a plurality of continuous image sections centered on the slice marker SM described above, and the function image data collected in the image sections intersecting the region of interest. A rectangular frame indicating the region of interest is added to the thumbnail data, and the thumbnail data of the functional image data collected in the image section corresponding to the slice marker SM is surrounded by a thick frame.

  FIG. 9C shows morphological image data (c-1) and functional image data (c-2) collected in the image cross section corresponding to the slice marker SM. For example, the full width at half maximum FWHM and the SUV value (see FIG. 9D) in the region of interest RO in which the slice marker SM is arranged are shown. In each of the MIP image data, the morphological image data, the functional image data, and the thumbnail data constituting the display data, a hot spot HP indicating the center of the disease area detected by the disease area detection unit 7 and a region of interest setting are provided. The region of interest RO set by the unit 8 is displayed in a superimposed manner.

  When the cine display mode is selected by the input unit 15 in the selection of the display mode, the slice marker superimposed on the MIP image data moves at a predetermined speed in the body axis direction, and in the image cross section coincident with the slice marker. Display data is generated based on the morphological image data and the functional image data. In this case, based on the display speed control signal supplied from the display speed control unit 12 described later, the movement speed of the slice marker in the region having the region of interest (the attention data collection region described later) is the region not including the region of interest. It is set slower than the moving speed in (non-attention data collection area). Then, the morphological image data and the functional image data are read from the data storage unit 91 at a reading speed corresponding to the display speed of the display speed control signal (that is, the movement speed of the slice marker), and are collected in the attention data collection area. The display speed of the morphological image data and the functional image data is set slower than the display speed of the morphological image data and the functional image data collected in the non-attention data collection area.

  On the other hand, when the selection of the fixed display mode and the setting of the position of the slice marker with respect to the MIP image data are performed in the input unit 15, the form collected in the image section corresponding to the slice marker as shown in FIG. Image data (c-1) and functional image data (c-2) are displayed together with the region of interest RO, hot spot HP, SUV value, and FWHM, and further, at the position of the image cross section as shown in FIG. 9B. Thumbnail data of functional image data with a thick frame added is displayed. If the position of the slice marker is updated by the input unit 15, new display data is generated based on the morphological image data, functional image data, thumbnail data, etc. corresponding to the updated slice marker.

  Returning to FIG. 1, the display unit 10 includes a conversion processing unit and a monitor (not shown), and the conversion processing unit performs D / A conversion on the display data supplied from the data synthesis unit 94 of the display data generation unit 9. And conversion processing such as TV format conversion is performed and displayed on the monitor. The operator who has observed the display data generated by the display data generation unit 9 and displayed on the display unit 10 uses the input device of the input unit 15 to display MIP image data, morphological image data, and functional image data of the display data. The addition / deletion of the region of interest and the correction of the position and size can be performed as necessary. Then, display data is collected and displayed based on the changed region of interest.

  Next, the attention data area setting unit 11 shown in FIG. 1 is generated in the image slices S1 to SN or a part thereof by sequentially moving the slice markers SM shown in FIG. 9A in the body axis direction. When the morphological image data and the functional image data are displayed in cine, the position information of the region of interest set by the region-of-interest setting unit 8 with respect to the diseased region and the image cross-section forming unit 5 at an interval d in the body axis direction of the subject 150 Based on the position information of the formed image slices S1 to SN, a collection area of morphological image data and functional image data effective for diagnosis of a disease area surrounded by the region of interest is set as the attention data collection area.

  FIG. 10 is a diagram for explaining the attention data collection area set by the attention data area setting unit 11. Z1 to ZN are the body axis directions (Z-axis) of the subject 150 as already shown in FIG. The position coordinates of the image slices S1 to SN formed in the direction (d) in the interval d. When the image sections Sa1 to SaM, which are a part of the image sections S1 to SN, intersect with the three-dimensional region of interest RO set so as to surround the diseased area of the subject 150, the image sections Sa1 to SaM are included. The area is set as the attention data collection area, and the area other than the attention data collection area is set as the non-attention data collection area.

  Next, the display speed control unit 12 in FIG. 1 receives the region information on the attention data collection region and the non-attention data collection region supplied from the attention data region setting unit 11 and the slice marker generation unit 93 of the display data generation unit 9. The position information of the supplied slice marker is received. When the slice marker exists in the attention data collection region, the morphological image data and the functional image data in the image section corresponding to the slice marker are displayed at the first display speed SP1, and the slice marker collects the non-attention data collection. If present in the region, a display control signal for displaying the morphological image data and the functional image data in the image cross section corresponding to the slice marker at the second display speed SP2 higher than the first display speed SP1 is generated. To do. Then, the obtained display control signal is supplied to the slice marker generation unit 93 and the data synthesis unit 94 of the display data generation unit 9.

  On the other hand, the moving mechanism unit 14 includes a gantry rotating unit, a gantry moving unit, and a moving mechanism control unit (not shown), and the gantry rotating unit performs the X-ray tube 211 and the X-ray according to the gantry rotation control signal supplied from the moving mechanism control unit. The rotating gantry 23 of the morphological image information collecting unit 2 on which the detector 221 is mounted is rotated at high speed.

  The gantry moving unit is provided with an X-ray CT gantry unit having the morphological image information collecting unit 2 and a PET gantry unit having the functional image information collecting unit 3 on the floor according to the gantry movement control signal supplied from the moving mechanism control unit. The body 150 is moved in the body axis direction along the guide rail.

  The movement mechanism control unit supplies the gantry rotation control signal generated based on the imaging conditions and the volume data collection conditions supplied from the input unit 15 via the system control unit 16 to the gantry rotation unit, and sends the gantry movement control signal. Supply to the gantry moving part.

  FIG. 11 is a diagram for explaining the X-ray CT gantry and the PET gantry that are moved by the gantry moving part of the moving mechanism unit 14. As shown in FIG. A bed 131 having a top plate 13 on which 150 is placed is installed, and a guide rail 132 is disposed in the body axis direction (z direction) of the top plate 13. Then, an X-ray CT gantry 133 having the morphological image information collection unit 2 so that the examination target part of the subject 150 is arranged in the photographic field of the morphological image information collection unit 2 and the imaging field of the functional image information collection unit 3; The imaging position is adjusted by moving the PET gantry 134 having the functional image information collection unit 3 in the body axis direction along the guide rail 132.

  Next, the input unit 15 of FIG. 1 includes an input device such as a keyboard, a selection switch, and a mouse, and a display panel, and forms an interactive interface when used in combination with the display unit 10. Then, input of subject information, input of administration drug information, selection of display mode, setting of display speeds SP1 and SP2, setting of imaging conditions and volume data collection conditions, setting of image data generation conditions and display data generation conditions, display Setting of data display conditions, setting of region of interest conditions, setting of threshold value α, threshold value β1 and threshold value β2, input of various instruction signals, and the like are performed using the above-described display panel and input device. In particular, the above-described threshold values include the performance of the functional image information collection unit 3, the dose of the radioisotope, the time from when the radioisotope is administered until the volume data is collected, the reconstruction processing method, and the subject 150. It is set based on the part to be examined.

  On the other hand, the system control unit 16 includes a CPU and a storage circuit (not shown), and the input information, selection information, and setting information supplied from the input unit 15 are stored in the storage circuit. Then, the CPU comprehensively controls each unit provided in the medical image diagnostic apparatus 100 based on the information read from the storage circuit, and generates morphological volume data and functional volume data, and morphological image data and functional image. Data generation, display data generation based on these image data, display speed control for the morphological image data and functional image data collected in the attention data collection area and the non-attention data collection area are executed.

(Display data generation / display procedure)
Next, the generation / display data is generated by using the form volume data and the function volume data generated by the form image information collection unit 2 and the function image information collection unit 3 of the present embodiment and stored in the volume data storage unit 4 in advance. The display procedure will be described along the flowchart of FIG. However, here, a case where the cine display mode is selected as the display mode will be described.

  Prior to the generation of display data, the operator of the medical image diagnostic apparatus 100 inputs subject information at the input unit 15 and then selects a cine display mode and sets display speeds for the attention data collection area and the non-attention data collection area. Then, setting of image data generation conditions and display data generation conditions, setting of display data display conditions, setting of region of interest conditions, setting of threshold value α, threshold value β1, threshold value β2, etc. are performed (step S1 in FIG. 12). These input information, selection information, and setting information are stored in the storage circuit of the system control unit 16.

  When the above initial setting is completed, the operator inputs a display data generation start instruction signal at the input unit 15, and this instruction signal is supplied to the system control unit 16 to start display data generation. (Step S2 in FIG. 12).

  That is, the disease candidate region detection unit 71 of the disease region detection unit 7 that has received the display data generation start instruction signal via the system control unit 16 sets the voxel value of the functional volume data read from the functional volume data storage unit 42. Multi-dimensional SUV data is generated by multiplying the body weight / radioisotope dose of the subject 150, and filtering processing for noise removal and smoothing is performed on the obtained SUV data. Then, one or a plurality of disease candidate regions are detected by comparing the voxel value of the filtered SUV data with the threshold value α.

  On the other hand, the disease region determination unit 72 of the disease region detection unit 7 applies orthogonal coordinates XYZ with the origin of the center of the disease candidate region detected by the disease candidate region detection unit 71 to the SUV data after the filtering process. The profile data in the X-axis direction to the Z-axis direction is generated by extracting the voxel values of the SUV data existing on each axis. Next, a disease region having a true disease is detected from the disease candidate regions by comparing the half-value width FWHM of the profile data with a predetermined threshold (lower limit) β1 and threshold (upper limit) β2 (FIG. 12 step S3).

  Next, the region-of-interest setting unit 8 includes the region-of-interest condition supplied from the input unit 15 via the system control unit 16 and the center position information (hot spot position) of the disease region supplied from the disease region determination unit 72 described above. 3D having a predetermined shape and size for the disease area of the morphological volume data stored in the morphological volume data storage unit 41 and the functional volume data stored in the functional volume data storage unit 42 based on the information) Is set (step S4 in FIG. 12).

  On the other hand, the image cross-section forming unit 5, for example, N image cross-sections (axial) perpendicular to the body axis direction (z-axis direction) of the subject 150 based on the image data generation conditions initially set in step S <b> 1 described above. (Section) S1 to SN are formed (step S5 in FIG. 12).

  When the formation of the image slice by the image slice forming unit 5 is completed, the morphological image data generating unit 61 of the image data generating unit 6 adds the image to the morphological volume data read from the morphological volume data storing unit 41 of the volume data storing unit 4. The form of the display data generation unit 9 represents N morphological image data generated by setting the image cross sections S1 to SN supplied from the cross section forming unit 5 and extracting the voxels of the morphological volume data existing in these image cross sections. The image data is stored in the image data storage unit 912. Similarly, the functional image data generation unit 62 generates N pieces of functional image data generated by setting the image slices S1 to SN in the functional volume data read from the functional volume data storage unit 42. The function image data storage unit 911 stores the function volume data read from the function volume data storage unit 42 and projects the maximum value onto the projection plane perpendicular to the front direction and the side surface direction of the subject 150. The MIP image data in the front direction and the side direction generated thereby is stored in the MIP image data storage unit 913 of the display data generation unit 9 (step S6 in FIG. 12).

  On the other hand, the attention data region setting unit 11 includes the position information of the region of interest set by the region of interest setting unit 8 with respect to the disease region and the image formed by the image cross-section forming unit 5 at the interval d with respect to the body axis direction of the subject 150. Based on the position information of the cross section (axial cross section) S1 to SN, the collection area of the morphological image data and the functional image data effective for diagnosis of the disease area surrounded by the region of interest is set as the attention data collection area. An area other than the collection area is set as a non-attention data collection area (step S7 in FIG. 12).

  Then, the display speed control unit 12 includes the region information of the attention data collection region and the non-attention data collection region supplied from the attention data region setting unit 11 and the slice supplied from the slice marker generation unit 93 of the display data generation unit 9. Receives marker position information. When the slice marker exists in the attention data collection region, the morphological image data and the functional image data in the image section corresponding to the slice marker are displayed at the first display speed SP1, and the slice marker collects the non-attention data collection. If present in the region, a display control signal for displaying the morphological image data and the functional image data in the image cross section corresponding to the slice marker at the second display speed SP2 higher than the first display speed SP1 is generated. Then, the data is supplied to the slice marker generation unit 93 and the data synthesis unit 94 of the display data generation unit 9 (step S8 in FIG. 12).

  Next, the slice marker generation unit 93 of the display data generation unit 9 generates a slice marker having a moving speed corresponding to the display speed control signal supplied from the display speed control unit 12, and the thumbnail data generation unit 92 Thumbnail data is generated by reducing the functional image data in a predetermined range read from the functional image data storage unit 911 with reference to the position information of the slice marker supplied from the marker generation unit 93.

  Next, the data synthesizing unit 94 receives the position information of the slice marker supplied from the slice marker generating unit 93, and supplies the functional image data and the morphological image data in the image section that matches the slice marker from the display speed control unit 12. The functional image data storage unit 911 and the morphological image data storage unit 912 are read at a reading speed corresponding to the display speed of the displayed display speed control signal. Then, the functional image data and morphological image data described above, the MIP image data in the front direction and the side direction read from the MIP image data storage unit 913, and the thumbnail data generated by the thumbnail data generation unit 92 are combined. Furthermore, display data is generated by adding the half-value width FWHM of the profile data measured by the disease region detection unit 7, the SUV value of the functional volume data, and the like. The obtained display data is displayed on the monitor of the display unit 10 (step S9 in FIG. 12).

(Second Embodiment)
Next, a second embodiment of the present disclosure will be described. The medical image display apparatus according to the second embodiment is collected in advance in a morphological image information collection apparatus such as an X-ray CT apparatus or a functional image information collection apparatus such as a PET apparatus installed separately, and is supplied via a network or the like. A plurality of image slices are formed for the morphological volume data and functional volume data, and morphological image data and functional image data in each image slice are generated. Next, a disease candidate region is detected based on the SUV value of the SUV data obtained by processing the voxel value of the functional volume data, and the disease region is detected based on the profile data of the SUV data in this disease candidate region. Then, morphological image data and functional image data collected in an image cross section intersecting with a region of interest having a predetermined shape set so as to surround the disease region are displayed with priority.

  In the block diagram of FIG. 13 showing the overall configuration of the medical image display apparatus in the present embodiment, units having the same configuration and function as the unit of the medical image diagnostic apparatus 100 shown in FIG. Detailed description is omitted.

  That is, the medical image display apparatus 200 of this embodiment shown in FIG. 13 stores three-dimensional morphological image information (morphological volume data) collected in advance by a medical image diagnostic apparatus such as an X-ray CT apparatus or an MRI apparatus. A volume data storage unit 171, and a volume data storage unit 17 having a functional volume data storage unit 172 for storing three-dimensional functional image information (functional volume data) collected in advance by a medical image diagnostic apparatus such as a PET apparatus or a SPECT apparatus; Based on the above-described voxels in the image cross section of the form volume data and the functional volume data read from the volume data storage section 4, the image cross section forming unit 5 for forming a plurality of image cross sections for the form volume data and the function volume data. Multiple morphological image data and functional image data Further, based on the functional volume data supplied from the volume data storage unit 4 and the image data generation unit 6 that generates MIP image data in the front direction and the side direction of the subject 150 based on the functional volume data. A disease region detection unit 7 that detects a disease region of the subject 150 and a region of interest setting unit 8 that sets a region of interest of a predetermined size surrounding the disease region with respect to the functional volume data and the morphological volume data described above.

  In addition, the medical image display apparatus 200 includes the morphological image data, functional image data, and MIP image data generated by the image data generation unit 6, thumbnail data of the functional image data, and SUV values and profiles calculated by the disease region detection unit 7. A display data generation unit 9 that generates display data by adding a half-value width FWHM of the data, a display unit 10 that displays the display data generated by the display data generation unit 9, and a region of interest setting unit 8 Based on the position information of the region of interest and the position information of the image section formed in the image section forming unit 5, the attention data collection area in which morphological image data and functional image data effective for diagnosis of the disease area are collected is set. Attention data area setting unit 11 to perform, and morphological image data and functional images collected in the attention data collection area A display speed control unit 12 for controlling the display speed of the morphological image data and the functional image data collected in the area other than the data and the attention data collection area, and further input of object information, image data generation conditions, and display data An input unit 15a for setting generation conditions, setting display data display conditions, inputting various instruction signals, and the like, and a system control unit 16a for comprehensively controlling each unit of the medical image display apparatus 200 are provided. .

  The input unit 15 a includes an input device such as a keyboard, a selection switch, and a mouse, and a display panel, and forms an interactive interface when used in combination with the display unit 10. Then, input of object information, selection of display mode, setting of display speeds SP1 and SP2, setting of image data generation conditions and display data generation conditions, setting of display data display conditions, setting of region of interest conditions, threshold value α, threshold value Setting of β1 and threshold β2, input of various instruction signals, and the like are performed using the above-described display panel and input device. In particular, the threshold α, the threshold β1, and the threshold β2 are collected from the performance of the medical diagnostic imaging apparatus that has generated the functional volume data, the dose of the radioisotope when the functional volume data is generated, and the volume data after the radioisotope is administered. It is set based on the time until it is performed, the reconstruction processing method, the examination target part, and the like.

  On the other hand, the system control unit 16a includes a CPU and a storage circuit (not shown), and the above-described input information, selection information, and setting information supplied from the input unit 15a are stored in the storage circuit. The CPU comprehensively controls each unit provided in the medical image display device 200 based on the information read from the storage circuit, generates morphological image data and functional image data, and based on the image data. Generation of display data, display speed control for the morphological image data and functional image data collected in the attention data collection area and the non-attention data collection area are executed.

  The display data generation / display procedure in this embodiment is the same as the display data generation / display procedure in the first embodiment shown in FIG.

  According to the first embodiment and the second embodiment described above, when diagnosing a disease region using a lot of morphological image data and functional image data collected from a subject, generation of these image data is performed. By focusing on the disease area automatically detected based on the three-dimensional image information (volume data) used for the image, it is possible to reduce the time required for interpretation and reduce the risk of oversight of the disease area. It becomes.

  In particular, the image is displayed so that the display speed of the image data collected in the image cross section intersecting with the region of interest set for the disease area is slower than the display speed of the image data collected in the other image cross section. By controlling the display speed of the data, it is possible to observe the diseased region in more detail without spending a lot of time for interpretation of all the image data.

  Further, since desired morphological image data and functional image data can be selected based on the thumbnail data displayed in a list centered on the above-mentioned region of interest, it becomes possible to extract these image data in a short time, The time required for interpretation is greatly reduced.

  Further, by manually or automatically setting a slice marker for the region of interest of the MIP image data generated based on the volume data, the thumbnail data centered on the position of the slice marker and the slice Since the morphological image data and the functional image data in the image cross section corresponding to the marker are automatically displayed, efficient image diagnosis is possible, and the burden on the operator in interpretation is reduced.

  Further, according to the first embodiment and the second embodiment described above, the disease candidate region is detected by comparing the pixel value of the image data with a predetermined threshold value, and the pixel value profile data in the disease candidate region. Since the disease region is determined by comparing the region width with a predetermined threshold, the true disease region can be automatically detected accurately and in a short time.

  On the other hand, according to the above-described second embodiment, generation and display of morphological image data and functional image data are performed based on volume data of a subject supplied from a medical image diagnostic apparatus installed separately via a network or the like. Therefore, the operator of the medical image display apparatus can easily obtain image information effective for diagnosis of the subject without much restrictions on time and place.

  As mentioned above, although 1st Embodiment and 2nd Embodiment of this indication were described, this indication is not limited to the above-mentioned embodiment, It can change and implement. For example, in the first embodiment described above, a medical image having the morphological image information collecting unit 2 that collects morphological volume data by X-ray CT imaging and the functional image information collecting unit 3 that collects functional volume data by PET imaging. Although the diagnostic apparatus 100 has been described, the morphological image information collection unit 2 may collect morphological volume data by MRI imaging, and the functional image information collection unit 3 may collect functional volume data by SPECT imaging. Good. However, when detecting diseased areas using volume data collected by SPECT imaging, it is desirable to use volume data that has been subjected to scattered ray correction or attenuation correction.

  In the first embodiment and the second embodiment described above, a two-dimensional form in a plurality of image cross sections (axial cross sections) perpendicular to the body axis direction of the subject 150 based on the form volume data and the function volume data. Although the case of generating image data and functional image data has been described, it may be an image cross section (coronal cross section or sagittal cross section) parallel to the body axis direction, or morphological image data and functional image data in an arbitrary image cross section.

  Display data using morphological image data and functional image data collected in the same image section, MIP image data to which a slice marker indicating the display section is added, and thumbnail data centered on the image data of the region of interest However, the present invention is not limited to this. For example, the thumbnail data in the cine display mode display data is not necessarily required. Further, display data may be generated using either morphological image data or functional image data.

  Furthermore, although the case where a disease candidate area | region and a disease area | region are detected based on the voxel value and SUV value of functional volume data was described, even if a disease candidate area | region and a disease area | region are detected based on the voxel value of form volume data Good.

  In the above-described embodiment, the method of repeating the update of the orthogonal coordinate system until any of the half-value width FWHMx to half-value width FWHMz of the profile data is larger than the threshold value β1 and smaller than the threshold value β2 has been described. It is not limited to the above method. For example, the profile data generation unit 722 of the disease region determination unit 72 illustrated in FIG. 6 has a plurality of directions (for example, six directions to approximately) formed radially around the center of gravity of the disease candidate region detected by the region center detection unit 721. Profile data is generated in (12 directions), and the FWHM comparison unit 723 compares the half-value width of these profile data with the threshold value β1 and the threshold value β2. When the number of profile data having a half width greater than the threshold value β1 and smaller than β2 is greater than the preset Nx, the disease candidate region is determined as a disease region, and when smaller than Nx, it is determined as a non-disease region. . The disease region can also be determined by such a method.

  On the other hand, since the temporal transition of the amount of radioisotope administered into the body is an important criterion for the disease area, two different time phases (for example, the early phase 1 hour after administration of the radioisotope and In recent years, a method for diagnosing a diseased region by introducing a so-called delayed scanning method for comparing image data collected in a delayed phase after 2 hours) has come to be performed. In such a case, the position information of the region of interest and the hot spot may be detected based on the functional volume data of the early layer having good image information, and these positional information may be set as the functional volume data of the delay layer. By such a method, it is possible to prevent the risk of overlooking the diseased area in the delay layer image data.

  In the above-described embodiment, the functional image information collection unit (PET imaging unit) 3 using the scintillator as a detector has been described. However, a semiconductor such as CdTe may be used as the detector. By using such a semiconductor detector, it is possible to directly convert annihilation gamma rays into electrical signals, so that energy resolution can be improved.

  Note that each unit included in the medical image diagnostic apparatus 100 or the medical image display apparatus 200 according to the present embodiment includes, for example, a computer including a CPU, a RAM, a magnetic storage device, an input device, a display device, and the like as hardware. It can also be realized by using. For example, the system control unit 16 that controls the medical image diagnostic apparatus 100 or the system control unit 16a that controls the medical image display apparatus 200 causes a processor such as a CPU mounted on the computer to execute a predetermined control program. Various functions can be realized. In this case, the above-described control program may be installed in advance in the computer, or may be stored in a computer-readable storage medium or installed in the computer of the control program distributed via the network. .

  Although several embodiments of the present invention have been described above, these embodiments are presented as examples and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

2 ... Morphological image information collection unit 21 ... X-ray generation unit 22 ... Projection data generation unit 25 ... Morphological volume data generation unit 3 ... Functional image information collection unit 31 ... Detector module 32 ... Detection data processing unit 33 ... Morphological volume data generation Unit 4 ... Volume data storage unit 41 ... Configuration volume data storage unit 42 ... Function volume data storage unit 5 ... Image section formation unit 6 ... Image data generation unit 61 ... Configuration image data generation unit 62 ... Function image data generation unit 63 ... MIP Image data generation unit 7 ... disease region detection unit 8 ... region of interest setting unit 9 ... display data generation unit 10 ... display unit 11 ... attention data region setting unit 12 ... display speed control unit 13 ... top plate 14 ... movement mechanism unit 15, 15a ... input unit 16, 16a ... system control unit 100 ... medical image diagnostic apparatus 200 ... medical image display apparatus

Claims (12)

In a medical image diagnostic apparatus for generating and displaying image data in a plurality of different image sections based on volume data collected from a subject,
Image data generating means for generating image data in the image slice set for the volume data;
A disease region detection means for detecting a disease region based on a voxel value of the volume data;
A region-of-interest setting means for setting a region of interest of a predetermined shape for the disease region of the volume data;
Display data generating means for generating display data for intensively displaying the image data generated in the image section intersecting with the region of interest;
A medical image diagnostic apparatus comprising: display means for displaying the display data.   Display speed control for controlling the display speed of each image data so that the display speed of the image data generated in the image cross section intersecting with the region of interest is slower than the display speed of the image data generated in the other image cross section. The medical image diagnostic apparatus according to claim 1, further comprising: a display unit configured to generate the display data based on a display speed control signal supplied from the display speed control unit.   Volume data storage means, wherein the display data generation means reads the display data by reading voxels in the image section of the volume data stored in the volume data storage means at a reading speed corresponding to the display speed. The medical image diagnostic apparatus according to claim 2, wherein the medical image diagnostic apparatus is generated.   MIP image data generating means for generating MIP (maximum intensity projection) image data based on the volume data, and slice marker generating means for generating a slice marker indicating the position of the displayed image cross section, the display data generating means Is based on the MIP image data on which the slice marker moving in a predetermined direction at a movement speed corresponding to the display speed is superimposed, and the image data in the image cross section indicated by the slice marker. The medical image diagnostic apparatus according to claim 2, wherein the medical image diagnostic apparatus is generated.   MIP image data generating means for generating MIP image data based on the volume data, slice marker generating means for generating a slice marker indicating the position of the displayed image cross section, and the image cross section indicated by the slice marker. Thumbnail data generating means for generating thumbnail data based on the image data in a plurality of image cross-sections at the center is provided. The display data generating means includes MIP image data on which the slice marker is superimposed, and the slice marker. The medical image diagnosis apparatus according to claim 1, wherein the display data is generated based on the image data in the image slice and the thumbnail data.   The disease region detection means includes a disease candidate region detection means for detecting a candidate region of a diseased part based on a voxel value of the volume data, and a disease for determining a disease region based on profile data of a voxel value in the candidate region The medical image diagnostic apparatus according to claim 1, further comprising an area determination unit.   The medical image diagnostic apparatus according to claim 6, wherein the display data generation unit adds at least half-width information of the profile data to the display data.   2. The medical image according to claim 1, wherein the image data generation unit generates the image data based on the volume data collected by at least one of morphological image information collection unit and functional image information collection unit. Diagnostic device.   The disease area detection means detects the disease area based on three-dimensional SUV (standardized uptake value) data obtained by processing the volume data collected by the functional image information collection means or voxel values of the volume data. The medical image diagnostic apparatus according to claim 1, wherein:   The morphological image information collecting means is either an X-ray CT imaging means or an MRI imaging means, and the functional image information collecting means is either a PET imaging means or a SPECT imaging means. A medical image diagnostic apparatus according to claim 8 or claim 9. In a medical image display device for generating and displaying image data in a plurality of different image cross sections based on volume data of a subject collected in advance by a medical image diagnostic device,
Image data generating means for generating image data in the image slice set for the volume data;
A disease region detection means for detecting a disease region based on a voxel value of the volume data;
A region-of-interest setting means for setting a region of interest of a predetermined shape for the disease region of the volume data;
Display data generating means for generating display data for intensively displaying the image data generated in the image section intersecting with the region of interest;
A medical image display device comprising: display means for displaying the display data. For a medical diagnostic imaging apparatus that generates and displays image data in a plurality of different image sections based on volume data collected from a subject.
An image data generation function for generating image data in the image section set for the volume data;
A disease region detection function for detecting a disease region based on the voxel value of the volume data;
A region-of-interest setting function for setting a region of interest of a predetermined shape for the disease region of the volume data;
A display data generation function for generating display data for intensively displaying image data generated in the image cross section intersecting with the region of interest;
A control program for executing a display function for displaying the display data.

Images