JP5060720B2 - Diagnosis support apparatus, method, and computer program - Google Patents

Description

  The present invention relates to a technique for supporting diagnosis of a living organ having a lumen and moving.

  Conventionally, a tomographic image of a living organ such as a heart is taken non-invasively and analyzed to be useful for a doctor's diagnosis. As one of the techniques, an electrocardiogram-gated myocardial SPECT method (Single Photon Emission Computed Tomography) is known. Thereby, the motion of the left ventricle can be analyzed in synchronization with the motion of the heart (for example, Non-Patent Document 1).

As a method for evaluating a myocardial SPECT image, a bull's eye map in which short-axis tomographic images of myocardial SPECT are superimposed is known. Further, as one of analysis methods using the bullseye map, a method of dividing the bullseye map into 17 segments and grasping the myocardial blood flow of each segment based on an image of a region corresponding to each segment of the bullseye map. Is known (for example, Non-Patent Document 2).
ECG-synchronized myocardial SPECT method, its basics and clinical application (Medical Sense, Inc. Tomoaki Nakata, Kenichi Nakajima, published on November 11, 2000) Standardized Myocardial Segmentation and Nomenclature for Tomographic Imaging of the Heart: A Statement for Healthcare Professionals From the Cardiac Imaging Committee of the Council on Clinical Cardiology of the American Heart Association (Circulation January 29,2002 p538-542)

  In the ECG-synchronized myocardial SPECT method, it is possible to grasp the volume change in the entire left ventricle, but even if there is an abnormality in the local myocardium, the location of the abnormality cannot be objectively specified.

  In addition, in the analysis with the conventional bullseye map, it is possible to detect a portion where the blood flow of the myocardium is abnormal, but it is impossible to locally grasp the change in the volume of the left ventricle due to this abnormality.

  Therefore, an object of the present invention is to provide a technique for displaying a change in the local motion state of a living organ and assisting a doctor's diagnosis.

  According to one embodiment of the present invention, there is provided a diagnostic support apparatus for displaying a state of a living organ having a lumen and moving, and relates to each segment when the organ wall of the organ is divided into a plurality of predetermined segments. Storage means for storing time-series data indicating the state change of the living organ, and display means for displaying the state change of the living organ related to the segment based on the time-series data.

  In a preferred embodiment, the time-series data is time-series data indicating the capacity of a plurality of partial spaces of the lumen, each of which is associated with each segment, and the display means displays the capacity of each partial space. You may make it display the curve which shows a time change.

  In a preferred embodiment, the time-series data is time-series data of pixel values extracted from a tomographic image obtained by imaging the living organ, and is the largest pixel in the organ wall region image belonging to each segment for each segment. Time-series data indicating values, and the display means may display a curve based on a change in the maximum pixel value of each segment.

  In a preferred embodiment, the display means displays a selection region for accepting selection of one or a plurality of segments among the plurality of segments and a change in the state of the living organ related to the segment selected in the selection region. The area to be displayed may be displayed.

  In a preferred embodiment, the living organ is a heart, and the plurality of segments are segments of the myocardium based on a dominant region of the coronary artery of the heart, and the selected region is in a bullseye map format. You may make it receive selection of each segment.

  In a preferred embodiment, the living organ is a heart, and the plurality of segments are obtained by segmenting a myocardium based on a dominant region of a coronary artery of the heart, and the display means includes the time series data. The ES, TPE, and TPF for each segment obtained from the above may be displayed.

  Hereinafter, a system for analyzing movement of a living organ according to an embodiment of the present invention will be described with reference to the drawings. This system, especially for the heart, takes images based on the ECG-synchronized myocardial SPECT (Single Photon Emission Computed Tomography) method for analyzing myocardial blood flow and function, and using that image, myocardial motion Analyze the situation locally. Furthermore, in order to support a doctor's diagnosis, the myocardial motion state is output.

  First, FIG. 1 shows an overall configuration of a heart motion analysis system according to a first embodiment of the present invention. That is, this system includes a tomographic image reconstruction system 1 that captures a tomographic image of the heart and an image analysis system 10 that analyzes time-series image data captured by the tomographic image reconstruction system 1.

  In the tomographic image reconstruction system 1, a tomographic image of an object is reconstructed based on projection data captured from 64 directions by a SPECT imaging device (not shown). The SPECT images reconstructed by the tomographic image reconstruction system 1 are a left ventricular long-axis vertical tomogram (Vertical Long Axis), a long-axis horizontal tomogram (Horizontal Long Axis), and a short-axis tomogram (Short Axis). In the image analysis system 10 of the present embodiment, analysis is performed using a short-axis tomographic image (hereinafter referred to as an SA image) among these SPECT images.

  Here, the SA image used in the present embodiment will be described with reference to FIG. This system mainly targets the SA image of the left ventricle 100 of the heart. Therefore, as shown in the figure, the SA image 140 is an image of a cross section perpendicular to the straight line connecting the base portion 110 and the apex portion 120. As will be described later, a plurality of SA images 140 are obtained in a predetermined phase in one cycle of the heart motion. The distance between the SA images 140 is a predetermined slice interval d. Therefore, the number of SA images (the number of slices) reconstructed in each phase differs depending on the patient. For convenience of subsequent processing, the number of slices is normalized to a predetermined number as will be described later. Note that when the tomographic image reconstruction system 1 captures SA images by a predetermined number of slices with the slice interval d being variable, normalization described later is not necessary.

  In addition, the tomographic image reconstruction system 1 performs myocardial gated SPECT in which an SA image is captured in synchronization with the electrocardiogram. Therefore, for example, as shown in FIG. 3, the interval between R waves of the electrocardiogram (RR interval: one cycle of heart motion) is equally divided into N, and the SA image is obtained at a sampling period of 1 / N of the RR interval. Shoot. FIG. 2 shows a state at a certain phase (T = T1). This photographing is continuously performed for at least one period. The number of images for one cycle is the number of slices × N phases. In addition, although the example of N = 8 was shown in FIG. 3, other than this, N may be 16, 20, 32, etc.

  As described above, one or more SA images are sent from the tomographic image reconstruction system 1 to the image analysis system 10.

  The image analysis system 10 will be described with reference to FIG. 1 again. The image analysis system 10 is configured by, for example, a general-purpose computer system, and individual components or functions in the image analysis system 10 described below are realized by, for example, executing a computer program.

  The image analysis system 10 acquires a time-series SA image reconstructed by the tomographic image reconstruction system 1 and stores the image data storage unit 11 for storing this, and the outer contour and inner contour of the heart from each SA image. , A coordinate data storage unit 13 for storing coordinate data indicating the contour extracted by the contour extraction unit 12, and the capacity of the left ventricular lumen for each predetermined unit space using the coordinate data A unit space-specific lumen volume calculation unit 14, a volume data storage unit 15 that stores a unit-space-specific lumen volume, and each subspace and unit when the left ventricle is divided into predetermined subspaces. A subspace definition table 16 that defines a correspondence relationship with a space, a subspace processing unit 17 that converts data into data for each subspace, and data for each subspace output from the subspace processing unit 17 are stored. And minute space data storage unit 18, and an output processing unit 19 for outputting a subspace data stored in the partial space data storage unit 18.

  The contour extraction unit 12 detects the contour of the myocardium constituting the left ventricle from the image data of a plurality of SA images stored in the image data storage unit 11 according to the flowchart shown in FIG.

  First, the contour extraction unit 12 acquires one SA image from the image data storage unit 11 (S11). For the SA image acquired here, the contour extraction unit 12 extracts the outer contour and inner contour of the left ventricle, and specifies the center point of the inner contour (S12). Here, the outer contour, the inner contour, and the center point are all specified by coordinate values.

  For example, the contour extraction unit 12 analyzes the image data of the SA image 140 using a predetermined image processing method as shown in FIG. 5 and detects the outer contour 141 and the inner contour 142 of the left ventricle. The heart muscle is between the outer contour 141 and the inner contour 142 detected here, and the inner side of the inner contour 142 is the lumen of the left ventricle. Further, the contour extracting unit 12 provides a plurality of sampling points 145 and 146 (dots and symbols are shown one by one in the drawing) along the outer contour 141 and the inner contour 142. And the coordinate value on this SA image 140 is acquired about each sampling point 145,146. Further, the contour extracting unit 12 determines the center point 143 of the inner contour 142 using the coordinate value of the sampling point 146 of the inner contour 142. The center point 143, the outer contour 141, and the inner contour 142 may be automatically detected, specified by the operator without automatic detection, or may be corrected by the operator.

  The coordinate values of the sampling points 145 and 146 of the inner contour 141 and the outer contour 142 specified as described above and the coordinate value of the center point 143 are stored in the coordinate data storage unit 13 (S13).

  Incidentally, the tomographic image reconstruction system 1 reconstructs a plurality of SA images with one phase as shown in FIG. Therefore, the contour extraction unit 12 performs the above-described steps S11 to S13 for all SA images photographed in the same phase (S14).

  When the above processing is completed for all SA images in one phase, the above processing is repeated for SA images in other phases (S15). As a result, the above processing is executed for all SA images in all phases for one cycle, and the image data photographed by the tomographic image reconstruction system 1 is converted into coordinate data.

  Here, the number of SA images taken at the same time may differ depending on the patient. This is because if the slice width d, which is the interval between the SA images, is constant, the size of the heart differs for each patient. Therefore, for the convenience of the subsequent processing, the contour extraction unit 12 performs a process of normalizing in order to align the number of SA images photographed at the same phase with a predetermined number (S16).

  In this normalization, for example, an original image whose number is not 16 slices is aligned to 16 slices. First, a standardized slice width D for standardization to 16 is determined according to the slice width d at the time of shooting and the number of original images. Then, interpolation processing is performed based on the standardized slice width D and the coordinate data of each original image to obtain 16 standardized coordinate data.

  The contour extraction unit 12 stores the normalized data including the coordinate values of the 16 slices normalized in step S16 and the normalized slice width D in the coordinate data storage unit 13 (S17). Thereby, the coordinate data storage unit 13 stores the coordinate value of the sampling point 145 of the outer contour, the coordinate value of the sampling point 146 of the inner contour, and the center point 143 stored in step S13. Along with the coordinate values, standardized 16-slice inner contour, outer contour, and center point coordinate data are stored.

  Through the above processing, the image data acquired from the tomographic image reconstruction system 1 is converted into coordinate data such as an inner contour of 16 slices.

  Referring to FIG. 1 again, the unit space-by-unit-space lumen capacity calculation unit 14 calculates the volume of the left ventricular lumen based on the normalized coordinate values stored in the coordinate data storage unit 13. Here, the left ventricular lumen is divided into predetermined unit spaces, and the capacity is calculated for each unit space.

  Therefore, division into unit spaces will be described with reference to FIG. FIG. 6 is a diagram modeling the state of the left ventricular lumen in a certain phase, which is obtained from the coordinate data normalized to 16 slices by the above-described processing. Each slice 160 is a substantially circular cylinder having a normalized slice width D on a substantially circular inner contour 142. Then, the substantially circular surface 161 of each slice 160 is divided into predetermined unit areas. Here, a predetermined number of sectors centered on the center point 143 of each slice surface 161 is defined as a unit area. Further, in this embodiment, if one slice is divided into 48, the central angle of the sector is set to 7.5 degrees. The unit area is cut out clockwise by 7.5 degrees from a predetermined reference direction. In the present embodiment, this reference direction is the 3 o'clock direction in the SA image 140 as shown in FIG. The sector-shaped region having a thickness D is a unit space 165.

  The lumen capacity calculation unit 14 for each unit space calculates the capacity for each unit space 165 with respect to all 16 slices, and stores it in the capacity data storage unit 15. This specific processing procedure will be described with reference to the flowchart of FIG.

  First, the unit space-specific lumen capacity calculation unit 14 reads standardized coordinate data for one slice from the coordinate data storage unit 13 (S21). At this time, the standardized slice width D is also acquired. Then, as described above, each slice 160 is divided into 48 unit spaces 165 (S22). The lumen capacity calculation unit 14 for each unit space calculates the capacity of each unit space 165 divided here, and stores it in the capacity data storage unit 15 (S23, S24).

  The processes in steps S21 to S24 are repeated, and the process is executed for all 16 slices having the same phase (S25).

  Further, the lumen capacity calculation unit 14 for each unit space repeats the processes of steps S21 to S25, performs the above process for all data for one cycle, and calculates the capacity of the unit space 165 (S26).

  Here, an example of the data structure of the capacity data 150 stored in the capacity data storage unit 15 by the above processing is shown in FIG. For example, the capacity data of each 48 unit space for all 16 slices by phase is stored in a 16 × 48 array format ([1, 1] to [16, 48]) as shown in FIG. ing. Therefore, each unit space can be identified by the phase T and the array [X, Y].

  Next, an example of the partial space definition table 16 is shown in FIG. The partial space definition table 16 stores information for defining regions constituting each partial space when the left ventricular lumen is divided into a plurality of partial spaces. For example, in the present embodiment, in order to divide the left ventricular chamber into 17 partial spaces, the partial space definition table 16 shows the correspondence between each partial space and the unit spaces constituting the partial space. Yes. That is, FIG. 9A stores the correspondence between the number (1 to 17) of each partial space and each unit space. This defines each partial space in association with the data structure of the capacity data storage unit 15 of FIG. The partial spaces 1 to 12 have 4 rows and 8 columns, the partial spaces 13 to 16 have 4 rows and 12 columns, and the partial space 17 has 4 rows and 48 columns. For example, as shown in FIG. 9B, it can be seen that the unit spaces belonging to the partial space 1 are 32 unit spaces from the array [1,33] to [4,40].

  Here, the partial space of the present embodiment is associated with a plurality of segments obtained by segmenting the myocardium based on the path of the coronary artery of the heart. For example, typically, the partial space is associated one-to-one with 17 segments of the myocardium defined by AHA (American Heart Association) (segment numbers 1 to 17 correspond to the partial space numbers, respectively). Alternatively, the partial space may be associated with three segments determined according to three coronary artery control regions. Here, the three coronary arteries are LAD (left anterior descending branch), RCA (right coronary artery), and LCX (rotating branch), and each coronary artery control region has a segment number of 17 segments of AHA and is as follows: Corresponding to That is, each segment of LAD is 1, 2, 7, 8, 14, 13, 17; RCA is each segment of 3, 4, 9, 10, 15; and LCX is 5, 6, 11, 12, 16 Control the territory of each segment.

  Referring back to FIG. 1, the subspace processing unit 17 processes the capacity data stored in the capacity data storage unit 15 based on the definitions stored in the subspace definition table 16. For example, the subspace processing unit 17 executes a process for calculating a change in capacity and each index within one period for each subspace according to the flowchart of FIG.

  First, the subspace processing unit 17 refers to the subspace definition table 16 and specifies a unit space belonging to a certain target subspace. And the capacity | capacitance data in a certain phase of the unit space specified here are read (S31). Then, the capacity data read here is added to calculate the capacity of the entire target partial space (S32). The processes in steps S31 and S32 are sequentially applied to other phases, and the capacity at each phase of the target subspace is calculated. And this is performed about all the phases for 1 period (S33).

  Based on the capacity data in each phase of the target subspace obtained in steps S31 to S33, the subspace processing unit 17 calculates a capacity change curve for one cycle (S34). The change curve may be obtained by applying Fourier approximation or the like based on the capacity at each phase calculated by the above processing, for example. Further, the subspace processing unit 17 differentiates the capacity change curve obtained here to obtain the capacity change rate (S35). Further, the subspace processing unit 17 calculates various indexes indicating the operation characteristics of the target subspace based on the capacity change and change rate of the target subspace over one cycle obtained by the above processing (S36). . Then, the partial space processing unit 17 stores the partial space data related to the target partial space calculated in steps S34 to S36 in the partial space data storage unit 18 (S37).

  The above processing is performed for all partial spaces, and partial space data is obtained for all partial spaces (S38).

  Next, the output processing unit 19 acquires data for each partial space from the partial space data storage unit 18 and outputs the data to the display device 2 or the printing device 3. Here, an example of a screen displayed on the display device 2 by the output processing unit 19 is shown in FIG.

  A display screen 200 shown in FIG. 11 includes a volume change curve 210 of the left ventricle in one cycle of the heart, a volume change rate curve 220 obtained from the volume change curve 210, a segment display area 230, and a segment selection area 240. And a partial space data display area 250.

  Here, the segment display area 230 has the same display mode as a bullseye map which is one of the methods used in the functional analysis of the left ventricle. That is, the segment display area 230 displays a circular area divided so as to correspond to the 17 segments defined by the AHA as in the bull's eye map.

  The operator can select one or more segments using the segment display area 230 or the segment selection area 240. Here, when one or more segments are selected, the capacity change curve 210 and the capacity change rate curve 220 of the subspace corresponding to the selected segment are respectively displayed. When a plurality of segments are selected, the capacity change curve 210 and the capacity change rate curve 220 are displayed in an overlapping manner.

  In the partial space data display area 250, various data relating to the selected segment and the partial space corresponding to the selected segment are displayed.

  In the example of FIG. 11, the segment 10 is selected, and the capacity change curve 210 and the capacity change rate curve 220 are displayed for the partial space corresponding to the segment 10, and various data are displayed in the partial space data display area 250. Data is displayed.

  According to the present embodiment, it is possible to grasp the motion status of each left ventricular subspace synchronized with the electrocardiogram. In particular, when each subspace is associated with 17 segments of AHA, by grasping the temporal change and rate of change of the capacity of each subspace, the motion status of the myocardial segment corresponding to that subspace can be determined. I can know. For example, when the amount of change in capacity or the rate of change in capacity is smaller than normal, it indicates that the function of the segment of the myocardium corresponding to the partial space is degraded. Therefore, in this case, it is estimated that some abnormality has occurred in the coronary artery associated with the segment.

  In the above embodiment, the image analysis system 10 acquires image data from the tomographic image reconstruction system 1, and performs various processes based on the acquired image data. However, in another embodiment, the processing performed by the image analysis system 10 may be divided into a plurality of systems. For example, it may be divided into a pre-stage system that performs up to the creation of unit space capacity data and a post-stage system that performs subsequent processes. In this case, the unit space capacity data storage unit 15 stores data generated by the preceding system.

  Here, if the format of the data stored in the unit space capacity data storage unit 15 is not in a format desired by the post-stage system, a predetermined space before the subspace processing unit 17 performs processing for each subspace. Data conversion may be performed. For example, when the unit space capacity data output by the preceding system is divided into 40 units per slice as a unit space, interpolation processing may be executed to reconfigure the unit space into 48 unit spaces per slice.

  Next, a second embodiment of the present invention will be described. In the following description, differences from the first embodiment will be mainly described, and description of the same configuration or function as in the first embodiment may be omitted.

  FIG. 12 is a diagram showing an overall configuration of a cardiac motion analysis system according to the second embodiment of the present invention. Then, the image analysis system 50 according to the present embodiment also performs processing using the SA image of one cycle or more supplied from the tomographic image reconstruction system 1 in the same manner as the image analysis system 10 of the first embodiment. Similar to the analysis system 10, data indicating the motion state of the myocardium is extracted.

  The image analysis system 50 is configured by, for example, a general-purpose computer system, and individual components or functions in the image analysis system 50 described below are realized by executing a computer program, for example.

  The image analysis system 50 includes an image data storage unit 11, a maximum count value detection unit 54 that detects the maximum count value for each unit region of the myocardial region of the SA image, and a maximum count value that stores the maximum count value for each unit region. From the storage unit 55, the segment definition table 56 that defines the correspondence between each unit region of the myocardium and a predetermined segment, and the maximum count value for each unit region stored in the maximum count value storage unit 55, To output the segment data stored in the segment-specific data storage unit 58 and the segment-specific data storage unit 58 for storing the segment-specific data, and the segment-specific maximum count value selection processing unit 57 for selecting the maximum count value in the segment Output processing unit 59. Furthermore, the image analysis system 50 may include the partial space data storage unit 18 of the first embodiment.

  The maximum count value detection unit 54 divides the myocardial region into a plurality of unit regions in the SA image, samples the pixels of each unit region, and selects the maximum count value (pixel value) from them.

  Here, the reason why the count value (pixel value) is used in the present embodiment is as follows. That is, because it is known that the count value (pixel value) of the image and the wall thickness of the myocardium are proportional to each other due to the partial volume effect, it is possible to know the motion state of the heart from the change in the maximum count value.

  FIG. 13 is a flowchart of the maximum count value detection process by the maximum count value detection unit 54. FIG. 14 is an explanatory diagram of processing for detecting the maximum count value from the SA image. Hereinafter, the processing of the maximum count value detection unit 54 will be described with reference to FIGS. 13 and 14.

  The maximum count value detection unit 54 first acquires one SA image and extracts the center point 143 of the left ventricular cross section, similarly to the contour extraction unit 12 of the first embodiment (S61, S62).

  Thereafter, the maximum count value for each unit area is extracted from the SA image and stored in the maximum count value storage unit 55 (S63, S64). For example, the maximum count value detection unit 54 samples a count value (pixel value) on a straight line from the center point 143 toward a predetermined reference direction, and selects the maximum count value among them. At this time, the maximum count value is a pixel of the myocardial region 148 between the outer contour 141 and the inner contour 142. The selection of the maximum count value is performed along a straight line rotated clockwise by a predetermined angle α from the reference direction around the center point 143. Hereinafter, for example, when α is set to 7.5 ° and this is repeated, a maximum count value of 48 can be obtained for one SA image.

  That is, in step S63, the myocardial region of the SA image is divided into a predetermined number of unit regions, the pixels of each unit region are sampled, and the maximum count value among them is selected.

  The above processing is applied to all SA images having the same phase (S65) as in the contour extracting unit 12 of the first embodiment (S65), and is applied to all data of one cycle (S66).

  Further, the data obtained by the above processing is normalized to 16 slices as in the contour extracting unit 12 of the first embodiment (S67). In this normalization, the maximum count value is also normalized by performing an interpolation process or the like. Then, the normalized coordinate data and maximum count value data of the center point are stored in the maximum count value storage unit 55 (S68).

  FIG. 15 shows an example of the data structure of the maximum count value storage unit 55.

  The maximum count value storage unit 55 is similar to the structure of the unit space capacity data 15 of the first embodiment. That is, for all 16 slices normalized, the myocardial region of each slice is divided into 48 unit regions, and the maximum count value is stored for each unit region.

  FIG. 16 shows an example of the data structure of the segment definition table 56.

  The segment definition table 56 has the same structure as the partial space definition table 16 of the first embodiment. That is, the 48 unit areas described above are associated with the 17 segments of AHA described in the first embodiment.

  The intra-segment maximum count value selection unit 57 selects the maximum count value of each segment according to the definition of the segment definition table 56.

  FIG. 17 is a flowchart of the processing by the intra-segment maximum count value selection unit 57.

  First, referring to the segment definition table 56, the maximum count value of the unit area belonging to the target segment is read from the maximum count value storage unit 55, and the maximum maximum count value in the segment is extracted (S71, S72). The processes in steps S71 and S72 are sequentially applied to other phases, and the maximum count value for one period of the target segment is extracted (S73).

  Based on the maximum count value in each phase of the target segment obtained in steps S71 to S73, the intra-segment maximum count value selection processing unit 57 calculates a change curve of the maximum count value for one cycle (S74). For example, the change curve may be obtained by applying Fourier approximation or the like based on the count value in each phase calculated by the above processing. Further, the intra-segment maximum count value selection processing unit 57 differentiates the change curve obtained here to obtain the change rate of the maximum count value (S75). Further, the intra-segment maximum count value selection processing unit 57 calculates various indexes indicating the operation characteristics of the target segment based on the change and rate of change of the target segment over one cycle obtained by the above processing (S76). ). Then, the intra-segment maximum count value selection processing unit 57 stores the data related to the target segment calculated in steps S74 to S76 in the segment-specific data storage unit 58 (S77).

  The above processing is performed for all segments, and segment data is obtained for all segments (S78).

  Next, the output processing unit 59 acquires the data for each segment from the segment-specific data storage unit 58 and outputs the data to the display device 2 or the printing device 3.

  FIG. 18 shows an example of a screen displayed on the display device 2.

  The display screen 300 includes a display area 310 for a maximum count value change curve for one cycle for each segment, a display area 320 for the change rate curve, a segment display area 330, a segment selection area 340, and a segment data display area 350. , A display switching instruction area 360, an auxiliary line display instruction area 370, and a global display selection area 380.

  The segment display area 330, the segment selection area 340, and the segment data display area 350 are the same as the segment display area 230, the segment selection area 240, and the segment data display area 250 of the first embodiment.

  In the maximum count value change curve display area 310, a change curve of the maximum count value of the segment selected in the segment display area 330 or the segment selection area 340 is displayed.

  In the maximum count value change rate curve display area 320, a change curve of the maximum count value of the segment selected in the segment display area 330 or the segment selection area 340 is displayed.

  The display switching instruction area 360 displays, in the display areas 310 and 320, the volume change and change rate for each partial space associated with each segment of the first embodiment, or each segment of the present embodiment. A switching instruction for whether to display another maximum count value change and change rate is accepted. That is, when the image analysis system 50 of the present embodiment further includes the partial space data storage unit 18 of the first embodiment, the output processing unit 59 displays according to the instruction received by the display switching instruction area 360. It is possible to switch data.

  The auxiliary line display instruction area 370 is an auxiliary line indicating ES (End Systole) in the change curve displayed in the maximum count value change curve display area 310, TPE (Time to peak ejection) at the fastest speed. This is an area for accepting selection of whether or not to display an auxiliary line indicating a contracted time) and an auxiliary line indicating a TPF (Time to peak filling: time expanded at the fastest speed). Since these auxiliary lines are displayed for each curve of each segment, it is possible to determine the synchrony of each region of the myocardium. That is, if the variation for each segment is small, it indicates that each region of the myocardium is moving in synchronism, and if the variation is large, it indicates that the movement of each region of the myocardium is shifted. These auxiliary lines can be displayed at the time of the capacity change curve and the capacity change rate curve of the first embodiment.

  Note that ES, TPE, and TPF are determined for each segment. For example, ES is the time when the capacity change curve takes the minimum value in the first embodiment, and the time when the change curve of the maximum count value takes the maximum value in the second embodiment. TPE is the time when the capacity change rate curve takes the minimum value in the first embodiment, and the time when the change rate curve of the maximum count value takes the maximum value in the second embodiment. TPF is the time when the capacity change rate curve takes the maximum value in the first embodiment, and the time when the change rate curve of the maximum count value takes the minimum value in the second embodiment.

  The global display selection area 380 is an area for receiving selection of display / non-display of the change curve and the change rate curve in the entire left ventricle. That is, when the volume change data is displayed in the display areas 310 and 320, the volume change and change rate of the entire left ventricle are displayed, and when the maximum count value data is displayed, the entire left ventricle is displayed. The maximum count value data is displayed.

  In the present embodiment, the change and change rate of the maximum count value for each segment are obtained and displayed, but instead, the local myocardial count change rate (% wall thicking) is calculated and this change curve or the like is calculated. May be displayed.

  The above-described embodiments of the present invention are examples for explaining the present invention, and are not intended to limit the scope of the present invention only to those embodiments. Those skilled in the art can implement the present invention in various other modes without departing from the gist of the present invention.

  For example, in the above-described embodiment, the heart motion is analyzed using the tomographic image of the heart, but the target object may be other than the heart as long as it has a lumen and moves periodically.

  In the above-described embodiment, the analysis using the SPECT image is performed, but the target image is not necessarily limited to this. For example, the second embodiment may use an RI (Radio Isotope) image other than SPECT, and the first embodiment may use an X-ray CT image, an MRI image, an ultrasonic image, etc. in addition to the RI image. Applicable.

  Furthermore, in the above-described embodiment, a system for analyzing and displaying data has been described. However, analysis and display may be performed by separate systems. For example, it is possible to configure a diagnosis support apparatus that includes only functions or configurations and data for displaying the display screens 200 and 300 of the first and second embodiments, and provides information that supports diagnosis by a doctor.

1 is a diagram showing an overall configuration of a cardiac motion analysis system according to a first embodiment of the present invention. It is a figure explaining the short-axis tomographic image (SA image) of the heart. It is a figure which shows the relationship between an electrocardiogram and the phase which images an SA image. It is a flowchart which shows the process which converts into the coordinate data of an outer outline and an inner outline from the image data of SA image. It is explanatory drawing of the sampling of the inner outline in an SA image, and an outer outline. It is explanatory drawing which shows how to cut out unit space. It is a flowchart which shows the capacity | capacitance calculation process according to unit space. 4 is a diagram illustrating an example of a data structure stored in a capacity data storage unit 15. FIG. It is a figure which shows an example of the structure of the segment definition table. It is a flowchart which shows the process sequence for calculating segment data. It is a figure which shows an example of the output screen of the system which concerns on this embodiment. It is a figure which shows the whole structure of the motion analysis system of the heart which concerns on the 2nd Embodiment of this invention. It is a flowchart of the detection process of the maximum count value. It is explanatory drawing of the process which detects the maximum count value from SA image. 6 is a diagram illustrating an example of a data structure of a maximum count value storage unit 55. FIG. 6 is a diagram illustrating an example of a structure of a segment definition table 56. FIG. It is a flowchart which shows the selection processing procedure of the largest count value in a segment. It is a figure which shows the other example of an output screen.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Tomographic image reconstruction system, 2 ... Display apparatus, 3 ... Printing apparatus, 10 ... Image analysis system, 140 ... Short-axis tomographic image (SA image), 12 ... Contour extraction process part, 14 ... Lumen capacity according to unit space Calculation unit, 17 ... segment processing unit, 19 ... output processing unit.

Claims (10)

A computer program for a diagnosis support apparatus for supporting diagnosis of a living organ having a lumen and moving,
First time-series data including capacities at different times of a plurality of partial spaces of the lumen respectively associated with each segment when the organ wall of the living organ is divided into a plurality of predetermined segments. Storing in the first storage means;
Displaying the curve indicating the temporal change in the capacity of the partial space associated with the segment based on the first time-series data stored in the first storage means, on the diagnosis support apparatus. A computer program to be executed. The computer program further includes:
Time-series data of pixel values extracted from a tomographic image obtained by imaging the living organ, wherein time-series data indicating the maximum pixel value of the organ wall region image belonging to each segment is stored in a second storage for each segment. Storing in the means;
2. The diagnostic support apparatus executes the step of displaying a curve based on a change in the maximum pixel value of the segment based on the second time-series data stored in the second storage unit. Computer program .   The computer program further includes:
  When a switching instruction is received when a curve indicating a temporal change in capacity of the partial space is displayed, the display is switched to display a curve based on a change in the maximum pixel value of the segment;
  When a switching instruction is received when a curve based on a change in the maximum pixel value of the segment is displayed, the display switching is performed so that a curve indicating a temporal change in the capacity of the partial space is displayed. The computer program according to claim 2, which is executed by a support device. The computer program further includes:
To display the selected area of the segment, and the step of accepting one or selection of a plurality of segments in the selected area,
The computer program according to any one of claims 1 to 3, which causes the diagnosis support apparatus to execute a step of displaying a curve indicating a temporal change in the capacity of the partial space associated with the segment selected in the selection region. . The living organ is a heart, and the plurality of segments are segments of the myocardium based on a dominant region of the coronary artery of the heart,
5. The computer program according to claim 4, wherein the selection area receives selection of each segment in a bullseye map format. The living organ is a heart, and the plurality of segments are segments of the myocardium based on a dominant region of the coronary artery of the heart,
The computer program further includes:
ES (End System: end systole time) , TPE (Time to peak ejection: time when contracted at the fastest speed) , TPF (Time to peak filling: fastest speed ) by segment obtained from the first time series data 6. The computer program according to claim 1 , further comprising: causing the diagnosis support apparatus to execute a step of displaying a time expanded in step 1). The computer program further includes:
Based on tomographic images obtained by imaging the living organs at different times and partial space definition information indicating regions constituting the plurality of partial spaces, the capacities at different times of the plurality of partial spaces are calculated, The computer program according to claim 1, which causes the diagnosis support apparatus to execute the step of generating first time-series data .   A computer-readable storage medium storing the computer program according to claim 1.   A diagnostic support apparatus for supporting diagnosis of a living organ having a lumen and moving,
  First time-series data indicating capacities at different times of a plurality of partial spaces of the lumen respectively associated with each segment when the organ wall of the living body organ is divided into a plurality of predetermined segments. First storage means for storing;
  Output processing means for displaying, on a display device, a curve indicating a temporal change in the capacity of the partial space associated with the segment, based on the first time-series data stored in the first storage means. Diagnosis support apparatus having.   A method performed by a diagnosis support apparatus for supporting diagnosis of a living organ having a lumen and moving,
  First time-series data including capacities at different times of a plurality of partial spaces of the lumen respectively associated with each segment when the organ wall of the living organ is divided into a plurality of predetermined segments. Storing in the first storage means;
  Displaying a curve indicating a temporal change in the capacity of the subspace associated with the segment based on the first time-series data stored in the first storage means.

Images