JP2008173387A - Ultrasonic diagnostic apparatus, ultrasonic image processing apparatus, and ultrasonic image processing program - Google Patents

Abstract

An ultrasonic diagnostic apparatus capable of detecting the contour of the intima of a heart without including papillary muscles and chordae and generating an image for evaluation of cardiac function.
By transmitting ultrasonic waves to the heart of a subject, a plurality of temporally continuous tomographic image data of the heart is acquired. In a tomographic image acquired at a predetermined time phase, the contour of the intima of the heart is designated without including papillary muscles or chordae. The contour position calculation unit 12 uses the designated contour as the initial contour, and obtains the position of the contour of the intima in each time phase by pattern matching between the two tomographic image data. The marker generation unit 11 generates a marker representing the contour of the intima in each time phase, and assigns a different color to each time phase marker. The display control unit 6 causes the display unit 7 to display a color image composed of markers at each time phase on the tomographic image.
[Selection] Figure 1

Description

  The present invention relates to an ultrasonic diagnostic apparatus that acquires an ultrasonic image in a subject using ultrasonic waves and analyzes the cardiac function using the ultrasonic images. In addition, the present invention relates to an ultrasonic image processing apparatus and an ultrasonic image processing program for analyzing a cardiac function using an ultrasonic image.

  As a method of diagnosing heart disease using an ultrasound diagnostic device, a tomographic image of the heart that changes over time is acquired, and the motion of the intima (the boundary between the heart muscle and blood) is automatically detected from the tomographic image. However, a method using a color kinematic image (CK image) for displaying the locus in color has been proposed. The CK image is a cross-sectional image of the heart that changes color every time along the intimal trajectory. When using a CK image, it is possible to observe the motion state of the left ventricular septum temporally and spatially with a single still image, and from the color composition ratio, the time phase of contraction of the left ventricular septum ( The degree of contraction delay).

  As a cardiac function evaluation method using the CK image, a method described in Patent Document 1 has been proposed. In the technique described in Patent Document 1, for example, a cross-sectional image of the left ventricle of a heart is divided into predetermined regions, each divided region is set as a region of interest, and in each set region of interest, at the time of maximum expansion of the heart The myocardial function is evaluated by calculating the ratio of the lumen cross-sectional area when a predetermined time elapses from the start of expansion with respect to the lumen cross-sectional area, and comparing the calculated ratio of the lumen cross-sectional area with the evaluation reference value. This technique is called ICK analysis.

  In this ICK analysis, for example, myocardial function is evaluated by using a CK image obtained by the method described in Patent Document 2. In the technique described in Patent Document 2, the contour of the intima is detected based on the brightness of the tissue and blood, and the locus of the intima is displayed in color to form a CK image.

JP 2003-325521 A JP-A-8-98837

  In the method described in Patent Document 2, the contour of the intima is detected based on the brightness of the tissue and blood. However, since the papillary muscles and chords in the vicinity of the intima also have high luminance values, the papillary muscles and chordae are also detected as intima according to the technique described in Patent Document 2. Thus, when trying to detect the contour of the intima based on the luminance of the tomogram, the papillary muscles and chords become noise, and it is difficult to detect the contour of the intima with high accuracy.

  In addition, when there is a total movement of the heart, the contour of the intima including the influence of the total motion is detected. Therefore, it is possible to accurately detect the contour of the intima in each time phase. It was difficult.

  As described above, according to the intima position detection method according to the prior art, it is difficult to accurately detect the contour of the intima, so that an error is included in the evaluation of myocardial function such as ICK analysis. Analysis was difficult.

  The present invention solves the above-mentioned problems, and can detect the contour of the intima of the heart without including papillary muscles and chordae, and can generate an image for evaluation of cardiac function. An object is to provide an ultrasonic diagnostic apparatus.

The invention according to claim 1 is an ultrasonic image acquisition means for acquiring a plurality of temporally continuous tomographic image data by scanning the heart of a subject with ultrasonic waves, and a tomographic image acquired at a predetermined time phase. The specification of the position of the contour of the intima of the heart with respect to the tomogram based on the image data is received, and the position of the contour of the intima in the tomogram based on the tomogram data acquired at each time phase other than the predetermined time phase is received. Contour position calculating means for each time phase obtained by pattern matching, and a marker representing the contour of the intima in each time phase are generated for each time phase, and each time phase marker has a different color for each time phase. An ultrasonic diagnostic apparatus comprising: a marker generating unit to be allocated; and a display control unit that displays the marker of each time phase to which the color is allocated on a tomographic image on a display unit.
The invention according to claim 7 receives a plurality of temporally continuous tomographic image data acquired by scanning the heart of the subject with ultrasonic waves, and further acquires a tomographic image acquired at a predetermined time phase. The specification of the position of the contour of the intima of the heart is received in the tomogram based on the data, and the position of the contour of the intima in the tomogram based on the tomogram data acquired in each time phase other than the predetermined time phase is received. Contour position calculating means for each time phase obtained by pattern matching, and a marker representing the contour of the intima in each time phase are generated for each time phase, and each time phase marker has a different color for each time phase. An ultrasonic image processing apparatus comprising: a marker generation unit to be allocated; and a display control unit that displays the marker of each time phase to which the color is allocated on a tomographic image so as to be displayed on a display unit.
According to the eighth aspect of the present invention, a computer receives a plurality of temporally continuous tomographic image data acquired by scanning the heart of a subject with ultrasonic waves, and is acquired at a predetermined time phase. The specification of the position of the contour of the intima of the heart is received in the tomogram based on the tomogram data, and the contour of the intima in the tomogram based on the tomogram data acquired in each time phase other than the predetermined time phase The contour position calculation function for obtaining the position of each time phase by pattern matching and the marker representing the contour of the intima in each time phase are generated for each time phase. An ultrasonic image processing program that executes a marker generation function that assigns different colors and a display control function that displays the markers of each time phase assigned with the colors on a tomographic image on a display device It is a non.

  According to the present invention, by specifying the contour of the intima without including papillary muscles and chordae, and determining the position of the contour in each time phase by pattern matching, each time without being affected by papillary muscles or chordae The position of the contour in the phase can be determined. Then, by assigning and displaying different colors for each time phase on the contour in each time phase, the intima position variation information is displayed so as to be identifiable by color, so that an image suitable for cardiac function evaluation can be obtained. .

[First Embodiment]
(Constitution)
The configuration of the ultrasonic diagnostic apparatus according to the first embodiment of the present invention will be described with reference to FIG. FIG. 1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to the first embodiment of the present invention.

  The ultrasonic probe 2 has a one-dimensional ultrasonic probe in which a plurality of ultrasonic transducers are arranged in a line in a predetermined direction (scanning direction), or a two-dimensional arrangement of a plurality of ultrasonic transducers in two dimensions. A dimensional ultrasonic probe is used. The transmission / reception unit 3 includes a transmission unit and a reception unit. The transmission unit performs transmission focus with a delay when transmitting ultrasonic waves, and supplies an electric signal to each ultrasonic transducer of the ultrasonic probe 2 to generate ultrasonic waves. The receiving unit amplifies echo signals received by the respective ultrasonic transducers of the ultrasonic probe 2, performs A / D conversion, and then adds and adds a delay time necessary for determining reception directivity. By the addition, the reflection component from the direction according to the reception directivity is emphasized.

  The image generation unit 4 includes a signal processing unit including a B-mode processing unit, a CFM processing unit, and a Doppler mode processing unit, and a DSC. Based on the received signal received by the transmission / reception unit 3, tomographic image data, etc. Ultrasonic image data is generated. The B-mode processing unit performs band-pass filter processing on the signal sent from the transmission / reception unit 3, then detects the envelope of the output signal and performs compression processing by logarithmic transformation, so that the image of the amplitude information of the echo To do. The CFM processing unit visualizes moving blood flow information. Blood flow information includes information such as speed, dispersion, and power, and blood flow information is obtained as binarized information. The Doppler mode processing unit generates blood flow information by a pulse Doppler method or a continuous wave Doppler method. The DSC converts the data after signal processing represented by the scanning line signal sequence into data of a coordinate system based on the spatial coordinates (digital scan conversion processing). For example, the DSC performs a scan conversion process on the signal-processed data output from the B-mode processing unit, thereby obtaining B-mode image data (hereinafter referred to as “tomographic image data”) representing the tissue shape of the subject. May generate).

  The ultrasonic probe 2, the transmission / reception unit 3, and the image generation unit 4 correspond to an example of an ultrasonic image acquisition unit.

  The tomographic image data generated by the image generation unit 4 is stored in the storage unit 5. When the ECG signal of the subject is acquired, the control unit 9 receives the ECG signal (electrocardiogram waveform) from the outside of the ultrasonic diagnostic apparatus 1 and the timing when the tomographic image data is generated in the tomographic image data. Are stored in the storage unit 5 in association with each other.

  The ultrasound diagnostic apparatus 1 according to this embodiment acquires a plurality of temporally continuous tomographic image data (heart motion image data) representing the heart by scanning the heart of the subject with ultrasound. For example, by scanning the subject's heart with ultrasound over one cardiac cycle or more, a plurality of temporal tomographic image data (heart motion image data) is acquired over one cardiac cycle or more. When the ECG signal is acquired, the control unit 9 stores the tomographic image data in the storage unit 5 in association with the time phase received at the timing when the tomographic image data is generated. Accordingly, the time phase at which the tomographic image data is generated is associated with each of the plurality of tomographic image data and stored in the storage unit 5.

  The display control unit 6 reads the tomographic image data from the storage unit 5 and causes the display unit 7 to display a tomographic image based on the tomographic image data. For example, when the operator designates an arbitrary time phase using the operation unit 8, the display control unit 6 reads tomographic image data associated with the designated time phase from the storage unit 5, and based on the tomographic image data. A tomographic image is displayed on the display unit 7.

  The image processing unit 10 includes a marker generation unit 11 and a contour position calculation unit 12. The image processing unit 10 sets the initial contour designated on the tomographic image representing the heart as the contour of the intima of the heart, and performs pattern matching between two generated tomographic images with different time phases, so that each time phase The position of the intimal contour is determined.

  The marker generation unit 11 generates a marker representing the initial contour designated by the operator. When the display control unit 6 receives the marker representing the initial contour, the display control unit 6 causes the display unit 7 to display the marker on the tomographic image.

  Here, a method for specifying the initial contour will be described. First, the operator designates an arbitrary time phase using the operation unit 8. The display control unit 6 reads the tomographic image data generated at the time phase designated by the operator from the storage unit 5 and causes the display unit 7 to display the tomographic image based on the tomographic image data. In this embodiment, since the tomographic image data of the heart is acquired, the tomographic image of the heart is displayed on the display unit 7. For example, cross-sectional image data of the heart is acquired by transmitting and receiving ultrasonic waves, and the cross-sectional image of the heart is displayed on the display unit 7.

  The tomographic image of the heart shows the papillary muscles, chordae, etc. in addition to the intima of the heart. The operator observes a tomographic image of the heart (for example, a cross-sectional image of the heart) displayed on the display unit 7 so as not to include the papillary muscles and chords shown in the tomographic image of the heart. Specifies the contour of the intima. When the contour of the intima is designated in this way, the marker generation unit 11 uses the designated contour as an initial contour, and generates a marker representing the initial contour. The display control unit 6 causes the display unit 7 to display a marker representing the initial contour on the tomographic image. The contour designated by this initial contour is set in the contour position calculation unit 12 as the contour of the intima.

  As described above, when the intima contour is designated by the initial contour, the contour position calculation unit 12 performs pattern matching between two images using the speckle pattern for each tomographic image generated at each time phase. The position of the intimal contour designated by the initial contour is obtained, and the intimal contour is temporally tracked.

  For example, the contour position calculation unit 12 receives coordinate information of each point on the contour of the intima designated by the initial contour, and further, a tomographic image in which the initial contour is set (hereinafter referred to as “tomographic image A”). Two tomographic images that are temporally continuous using a speckle pattern by reading from the storage unit 5 tomographic image data (hereinafter sometimes referred to as “tomographic image data B”) generated By performing pattern matching between the tomograms A and the next tomogram B, a movement vector of each point on the intima contour designated by the initial contour is obtained. This movement vector represents the displacement of each point on the contour and the moving direction in which each point is displaced. That is, the contour position calculation unit 12 performs pattern matching between two tomographic images, and calculates a movement amount of speckles, thereby obtaining a movement vector of each point on the contour. Thus, by obtaining the movement vector of each point on the contour, the position of the contour of the intima in the time phase when the tomographic image data B next to the tomographic image A in which the initial contour is set is generated.

  Further, the contour position calculation unit 12 reads tomographic image data (hereinafter also referred to as “tomographic image data C”) generated next to the tomographic image data B from the storage unit 5 and uses the speckle pattern. The movement vector of each point on the intima contour is obtained by pattern matching between two consecutive tomographic images (tomographic image B and tomographic image C). Thereby, the position of the contour of the intima in the time phase when the tomographic image data C is generated is obtained.

  As described above, the movement vector at each point on the intimal contour designated by the initial contour is obtained for each time phase when each tomographic image data is generated by pattern matching using the speckle pattern. The movement vector at each point on the contour of the object is temporally tracked. As a result, the contour of the intima can be traced in time. For example, the contour position calculation unit 12 detects the contour of the intima for each time phase for all tomographic image data acquired over one cardiac cycle, and obtains the position of the contour of the intima in each time phase. Thereby, the contour position of the intima in each time phase is obtained over one cardiac cycle.

  When the position of the intima contour in each time phase is obtained by the contour position calculation unit 12, the marker generation unit 11 contours information indicating the intima contour in each time phase (coordinate information of each point on the contour). In response to the position calculation unit 12, a marker representing the contour of the intima in each time phase is generated. For example, when the intima contour in each time phase is detected over one cardiac cycle, the marker generator 11 generates a marker representing the intima contour for all time phases.

  Furthermore, the marker generation unit 11 assigns a different color for each time phase to the marker in each time phase. For example, the marker generation unit 11 assigns a color that is different in each time phase from the end systole to the end diastole of the heart to the corresponding time phase marker. For example, the color to be assigned to each time phase marker is determined in advance, and the correspondence between the time phase and the color is stored in advance in a storage unit (not shown). The marker generation unit 11 assigns a corresponding color to each time phase marker according to the association.

  The display control unit 6 receives a plurality of markers (hereinafter sometimes referred to as “color images”) assigned different colors for each time phase from the marker generation unit 11 and causes the display unit 7 to display them. At this time, the display control unit 6 reads the tomographic image data generated in the time phase designated by the operator from the storage unit 5 and displays the color image on the tomographic image based on the tomographic image data on the display unit 7. Let

  Since the color image is composed of a plurality of markers assigned different colors for each time phase, the motion state of the heart can be observed temporally and spatially with one tomographic image, From the color composition ratio, it becomes possible to know the time phase of the heart contraction (the degree of contraction delay, etc.).

  An example of a color image representing the contour of the intima generated as described above is shown in FIG. FIG. 2 is a diagram showing an image acquired by the ultrasonic diagnostic apparatus according to the first embodiment of the present invention and a result of cardiac function evaluation.

  When the operator designates an arbitrary time phase using the operation unit 8, the display control unit 6 reads the tomographic image data acquired at the designated time phase from the storage unit 5, and generates a tomogram based on the tomographic image data. The image is displayed on the display unit 7. Further, the display control unit 6 causes the display unit 7 to display a plurality of markers (color images) assigned different colors for each time phase on the tomographic image. For example, as shown in FIG. 2, the display control unit 6 displays the tomographic image 100 designated by the operator on the display unit 7 and displays the color image 101 on the tomographic image 100 in an overlapping manner.

  A tomographic image 100 shown in FIG. 2 represents a cross-sectional image of the heart acquired at the end diastole. The color image 101 is composed of a plurality of markers assigned different colors for each time phase. For example, it is composed of markers for one cardiac cycle. The motion state of the heart can be observed temporally and spatially by an image in which the tomographic image 100 and the color image 101 are displayed in an overlapping manner. Further, since each marker constituting the color image 101 is assigned a different color for each time phase, it is possible to know the time phase of the heart contraction (such as the degree of contraction delay) from the color composition ratio. it can. The color bar 102 represents the association between the color assigned to the marker and the time phase. Specifically, it represents the correspondence between the time from the start of the expansion of the heart and the color assigned to the marker. In this way, each marker represents the contour of the intima at each time phase, and since a different color is assigned to each marker for each time phase, the time phase of heart contraction ( The degree of contraction delay).

  In this embodiment, a color corresponding to the corresponding time phase is assigned and displayed on each time phase marker itself. Furthermore, in this embodiment, the display control unit 6 may interpolate and display the color between the markers by assigning the color assigned to the marker between the markers.

  As described above, the intima contour is specified so as not to include papillary muscles and chordae, and the intima contour at each time phase is detected by pattern matching between two tomographic images using a speckle pattern. Thus, the contour of the intima can be detected without being affected by papillary muscles or chordae. And, by assigning and displaying different colors for each time phase to the markers representing the intima contours of each time phase, the variation information of the intima position is displayed so that it can be identified by color, which is suitable for cardiac function evaluation It is possible to provide a simple image.

  The cardiac function evaluation using the tomographic image 100 and the color image 101 is performed by the cardiac function evaluation unit 20. Specifically, the cardiac function evaluation unit 20 performs cardiac function analysis (referred to as “ICK analysis”) described in Japanese Patent Laid-Open No. 2003-325521. This cardiac function analysis will be briefly described.

  For example, the cardiac function evaluation unit 20 sets the barycentric position in the cross-sectional image of the heart and draws a straight line radially from the barycentric position, thereby dividing the cross-sectional image into six. In the example shown in FIG. 2, a tomographic image 100 corresponding to a cross-sectional image is represented by int (lower wall): D1, pst (rear wall): D2, lat (side wall): D3, ant (front wall): D4, asp. (Front wall septum): D5, sp (rear wall septum): D6 divided into six regions. Then, the cardiac function evaluation unit 20 calculates the ratio of the cross-sectional area over time with respect to the cross-sectional area at the time of maximum expansion of the heart (dilatation area change rate) for each region of D1 to D6. In addition, the cardiac function evaluation unit 20 calculates the ratio of the cross-sectional area over time with respect to the cross-sectional area at the start of contraction of the heart (area change rate during contraction) for each region of D1 to D6. The cardiac function evaluation unit 20 obtains an area change rate during expansion and an area change rate during contraction based on the cross-sectional area that changes with time in each of the divided D1 to D6 regions.

  The cardiac function evaluation unit 20 calculates the ratio of the cross-sectional area when a predetermined time has elapsed from the start of expansion with respect to the area at the time of maximum expansion of the heart, and compares the calculated area ratio with the evaluation reference value. , Evaluate cardiac function. For example, the cardiac function evaluation unit 20 calculates an area change rate at the time of expansion when 30% has elapsed from the start of expansion, and compares the value with a preset evaluation reference value to determine whether the value is a normal value. Judge whether or not. Here, as an example, the rate of change in area at the time of expansion at 30% has been compared with the evaluation reference value. However, the rate of change in area at the time other than 30% was compared with the reference value for evaluation of cardiac function. Evaluation may be performed.

  Specifically, the cardiac function evaluation unit 20 calculates the internal area surrounded by the contour based on the contour of the intima in each time phase obtained by the image processing unit 10. This area is calculated by counting the number of dots in the portion surrounded by the contour of the intima. And the cardiac function evaluation part 20 calculates | requires the cross-sectional area in each time phase about each area | region D1-D6 divided into six, and the cross-sectional area in each time phase with respect to the cross-sectional area in the time of the maximum expansion for every area | region of D1-D6. The ratio (area change rate at the time of expansion) is obtained. Then, the cardiac function evaluation unit 20 determines whether or not the value is a normal value by comparing the area change rate at the time of expansion 30% after the expansion starts with a preset evaluation reference value.

  The cardiac function evaluation unit 20 creates the graph 110 and the band graph 120 shown in FIG. A graph 110 is a graph showing the position of the contour of the intima in the diastole. The vertical axis shows the ratio of the intima position with respect to the maximum expansion, and the horizontal axis shows time. 100% of the horizontal axis represents the maximum expansion time. The cardiac function evaluation unit 20 creates a graph for each of the areas D1 to D6. The band graph 120 indicates the position of the contour of the intima in each region. Also for the band graph 120, the cardiac function evaluation unit 20 obtains a graph for each of the areas D1 to D6. When the display control unit 6 receives the graph 110 and the band graph 120 from the cardiac function evaluation unit 20, the display control unit 6 displays them on the display unit 7 together with the tomographic image 100.

  Then, for example, when the time point at which 30% has elapsed from the start of expansion is designated by the operator, the display control unit 6 is positioned at the position corresponding to the time at which 30% has elapsed on the band graph 120 of each region. Is displayed. The elapsed time from the start of expansion can be specified on the color bar 102, or may be specified on the horizontal axis of the graph 110. The cardiac function can be evaluated by confirming the intima position indicated by the band graph of each region on the basis of the display position of the pointer 121 indicating 30% elapsed time.

  The operation unit 8 is configured by a keyboard, a mouse, a trackball, or a TCS (Touch Command Screen), and is used for designating an initial contour (the contour of the intima of the heart) and the initial contour by the operation of the operator. The time phase when the tomographic image was acquired is specified.

  In addition, each process by the image processing unit 10, the display control unit 6, and the cardiac function evaluation unit 20 may be realized by hardware or may be realized by software. For example, the image processing unit 10, the display control unit 6, and the cardiac function evaluation unit 20 are configured by a CPU and a storage device such as a ROM, a RAM, and an HDD. An image processing program for realizing the function of the image processing unit 10, a display control program for realizing the function of the display control unit 6, and a cardiac function evaluation for realizing the function of the cardiac function evaluation unit 20 in the storage device Remember the program. The CPU executes the image processing program stored in the storage device to realize the function of the image processing unit 10, and the display control program to execute the function of the display control unit 6 to evaluate the cardiac function. You may make it implement | achieve the function of the cardiac function evaluation part 20 by running a program.

(Ultrasonic image processing device)
Further, the contour of the intima of the heart at each time phase is obtained by the ultrasonic image processing apparatus including the storage unit 5, the display control unit 6, the display unit 7, the operation unit 8, the image processing unit 10, and the cardiac function evaluation unit 20. May be detected to generate a color image. That is, an ultrasonic image processing apparatus may be provided outside the ultrasonic diagnostic apparatus, and a color image may be generated by the ultrasonic image processing apparatus.

  In this case, a plurality of temporally continuous tomographic image data (moving image data of the heart) is obtained by scanning the heart with ultrasonic waves by an ultrasonic diagnostic apparatus according to the related art installed outside the ultrasonic image processing apparatus. To get. Then, the ultrasonic image processing apparatus receives a plurality of tomographic image data acquired by the ultrasonic diagnostic apparatus and causes the storage unit 5 to store the plurality of tomographic image data. In this way, a plurality of tomographic image data is acquired by the ultrasonic diagnostic apparatus installed outside the ultrasonic image processing apparatus and stored in the storage unit 5 of the ultrasonic image processing apparatus. Then, the image processing unit 10 detects the contour of the intima of the heart from the tomographic image data of each time phase by pattern matching between the two images using the spec pattern, and further determines the contour of the intima of each time phase. Assign a different color to the marker to be displayed for each time phase. The display control unit 6 causes the display unit 7 to display a marker (color image) assigned with a color on the tomographic image. The cardiac function evaluation unit 20 evaluates the cardiac function based on the color image.

  As described above, even when a color image representing the intimal outline of the heart at each time phase is generated by the ultrasonic image processing apparatus, the intimal outline is not affected by the papillary muscles or chordae. It becomes possible to detect. And, by assigning and displaying different colors for each time phase to the intima contour of each time phase, the intima position fluctuation information is displayed so as to be identifiable by color, which is suitable for cardiac function evaluation Images can be obtained.

(Operation)
Next, the operation of the ultrasonic diagnostic apparatus according to the first embodiment of the present invention will be described with reference to FIG. FIG. 3 is a flowchart for explaining a series of operations by the ultrasonic diagnostic apparatus according to the first embodiment of the present invention. In this embodiment, tomographic image data of the heart is acquired using the heart as a diagnostic site, and the contour of the intima of the heart that is used for the evaluation of cardiac function is detected based on the tomographic image data.

(Step S01)
First, the ultrasonic probe 2 is applied to a subject, ultrasonic waves are transmitted to the heart, and the image generation unit 4 generates a plurality of temporally continuous tomographic image data (heart moving image data). For example, by transmitting and receiving ultrasonic waves over one cardiac cycle or more, a plurality of tomographic image data that are temporally continuous over one cardiac cycle or more are generated. The control unit 9 receives an ECG signal from the outside of the ultrasound diagnostic apparatus 1 and stores the generated tomographic image data in the storage unit 5 in association with the time phase at which the tomographic image data was generated.

(Step S02)
Next, the operator uses the operation unit 8 to designate an analysis interval for performing cardiac function evaluation. For example, the systole or diastole of the heart is specified. In this embodiment, it is assumed that the diastole of the heart is designated.

(Step S03)
Next, the operator designates a time phase when a tomographic image for setting an initial contour is generated using the operation unit 8. For example, it is preferable to designate a time phase near the end systole of the heart and set an initial contour in a tomographic image generated at the end systole. This is because the contour detection accuracy is better when the initial contour is set for the tomographic image generated in the time phase near the end systole of the heart and the contour of the intima is traced from the end systole to the end diastole. In other words, since the brightness value of the lumen of the heart is low, when the contour of the intima is tracked from the end diastole to the end systole, the contour of the intima is tracked in a direction where the brightness value is low. As a result, an error may be included in the contour detection. Therefore, it is preferable to set an initial contour for the tomographic image generated at the end systole and track the contour of the intima.

(Step S04)
When the time phase is designated by the operator, the display control unit 6 reads the tomographic image data associated with the time phase from the storage unit 5 and causes the display unit 7 to display the tomographic image based on the tomographic image data. When the time phase near the end systole of the heart is designated, the display control unit 6 reads the tomographic image data associated with the time phase near the end systole from the storage unit 5 and displays the tomographic image near the end systole. 7 is displayed.

(Step S05)
In a state where a tomographic image near the end systole is displayed on the display unit 7, the operator uses the operation unit 8 to intimate the intima by the initial contour so that the papillary muscles and chords expressed in the tomographic image are not included. Specifies the outline of the. When the initial contour is designated by the operator, the marker generating unit 11 generates a marker representing the initial contour. The display control unit 6 causes the display unit 7 to display a marker representing the initial contour on the tomographic image near the end systole.

(Step S06)
The contour position calculation unit 12 reads the tomographic image data B generated next to the tomographic image A in which the initial contour is set from the storage unit 5 and reads between the two tomographic images using the speckle pattern (the tomographic image A and the tomographic image). By performing pattern matching of the image B), a movement vector of each point on the intima contour is obtained. For example, the contour position calculation unit 12 obtains a movement vector of each point on the contour of the intima in each time phase included in one cardiac cycle for all tomographic image data acquired over one cardiac cycle. The contour of the intima in each time phase is detected.

(Step S07)
When the marker generation unit 11 receives information (coordinate information of each point on the contour) indicating the contour of the intima in each time phase from the contour position calculation unit 12, the marker generation unit 11 generates a marker representing the contour of the intima in each time phase. To do. And the marker production | generation part 11 assigns a different color for every time phase to the marker of each time phase. For example, when the intima contour in each time phase is detected over one cardiac cycle, the marker generator 11 generates a marker representing the intima contour for all time phases.

(Step S08)
The display control unit 6 causes the display unit 7 to display a marker (color image) to which a different color is assigned for each time phase, overlaid on the tomographic image specified by the operator. For example, when the end diastole is designated by the operator, the display control unit 6 reads tomographic image data generated at the end diastole from the storage unit 5 and causes the display unit 7 to display a tomographic image based on the tomographic image data. Then, the display control unit 6 causes the display unit 7 to display the color image on the tomographic image at the end diastole. For example, as shown in FIG. 2, the color image 101 is displayed on the display unit 7 so as to overlap the tomographic image 100 at the end diastole. As described above, in the same manner as the CK image, the variation information of the intima position is output as an image that can be identified by color.

(Step S09)
As described above, when the contour of the intima in each time phase is obtained and a color image is generated, the cardiac function evaluation unit 20 performs ICK analysis (described in Japanese Patent Laid-Open No. 2003-325521) based on the color image. Analysis method).

  As described above, by specifying the contour of the intima so as not to include papillary muscles and chordae, and detecting the contour of the intima in each time phase by pattern matching between two images using a speckle pattern, It becomes possible to detect the contour of the intima without being affected by papillary muscles or chords. And, by assigning and displaying different colors for each time phase to the markers representing the intima contours of each time phase, the variation information of the intima position is displayed so that it can be identified by color, which is suitable for cardiac function evaluation It is possible to provide a simple image. By performing ICK analysis based on this color image, more appropriate evaluation is possible.

[Second Embodiment]
(Constitution)
Next, the configuration of an ultrasonic diagnostic apparatus according to the second embodiment of the present invention will be described with reference to FIG. FIG. 4 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to the second embodiment of the present invention. In the second embodiment, a process for removing the influence of the total movement of the heart is performed.

  In the ultrasonic diagnostic apparatus 1A according to the second embodiment, the configuration of the image processing unit 30 is different from the configuration of the image processing unit 10 of the ultrasonic diagnostic apparatus 1 according to the first embodiment. Since the configuration other than the image processing unit 30 is the same as that of the ultrasonic diagnostic apparatus 1 according to the first embodiment, the description thereof is omitted.

  The image processing unit 30 includes a contour position calculation unit 31, a contour movement speed calculation unit 32, a contraction center calculation unit 33, a contraction center movement speed calculation unit 34, a subtraction unit 35, a contour reconstruction unit 36, and a marker generation unit 37. ing.

  Similar to the contour position calculation unit 12 according to the first embodiment, the contour position calculation unit 31 sets the initial contour by performing pattern matching between two temporally continuous tomographic images using a speckle pattern. The movement vector of each point on the contour of the intima is obtained for each time phase. Thereby, the contour of the intima in each time phase is obtained. The contour moving speed calculation unit 32 calculates the moving speed of each point on the contour in each time phase based on the movement vector (displacement) of each point on the contour in each time phase and the time between each time phase. . For example, the contour position calculation unit 31 detects the contour of the intima for every tomographic image data acquired over one cardiac cycle, and the contour moving speed calculation unit 32 is included in one cardiac cycle. The moving speed of each point on the contour in each time phase is obtained.

  Based on the intima contour in each time phase calculated by the contour position calculator 31, the contraction center calculation unit 33 calculates, for example, the position of the center of gravity of the range surrounded by the intima contour as 1 of the contraction center position. As an example, it is calculated for each time phase. In this embodiment, it is not necessary to obtain the exact position of the contraction center, and the position near the contraction center may be obtained. As a method for calculating the center of gravity, a method according to the related art is used. Further, the contraction center calculation unit 33 calculates the center of gravity movement vector in each time phase as an example of the contraction center movement vector based on the position of the center of gravity in each time phase. The movement vector of the center of gravity (contraction center) represents the displacement of the position of the center of gravity (contraction center) and the movement direction in which the center of gravity (contraction center) is displaced. The contraction center moving speed calculation unit 34 calculates the moving speed of the center of gravity in each time phase based on the movement vector (displacement) of the center of gravity (contraction center) in each time phase and the time between each time phase, for example. Calculated as an example of moving speed.

  The subtraction unit 35 subtracts the movement speed of the contraction center obtained by the contraction center speed calculation unit 34 from the movement speed of each point on the intimal outline obtained by the contour movement speed calculation unit 32. At this time, the subtraction part 35 subtracts the moving speeds of the same time phase. That is, the subtracting unit 35 subtracts the moving speed of the contraction center in the same time phase from the moving speed of each point on the contour in each time phase to obtain a difference in moving speed in each time phase.

  In this embodiment, it is assumed that the position of the center of gravity in the range surrounded by the contour of the intima in each time phase is the position of the heart contraction center. Further, it is assumed that the moving speed of the contraction center position is equal to the speed of the whole heart movement. That is, it is assumed that the moving speed of the center of gravity is equal to the speed of the whole heart movement. Then, by subtracting the moving speed of the center of gravity from the moving speed of each point on the contour of the intima, the influence of the whole heart movement is removed.

  The contour reconstruction unit 36 obtains the position of the contour of the intima in each time phase based on the difference in moving speed in each time phase obtained by the subtraction unit 35. For example, the contour reconstruction unit 36 obtains the position of the contour of the intima in each time phase by integrating the difference in moving speed in each time phase with the time between each time phase. Since the speed of the whole heart and the assumed speed of movement of the center of gravity are subtracted from the speed of movement of each point on the contour of the intima, the contour of the intima from which the influence of the whole image has been removed is obtained. become.

  The subtraction unit 35 may subtract the movement vector of the contraction center obtained by the contraction center calculation unit 33 from the movement vector of each point on the intimal outline obtained by the contour position calculation unit 31. At this time, the subtraction unit 35 subtracts movement vectors having the same time phase. That is, the subtracting unit 35 subtracts the movement vector of the contraction center in the same time phase from the movement vector of each point on the contour in each time phase, and obtains the difference between the movement vectors in each time phase. In this case, the contour reconstruction unit 36 obtains the position of the intimal contour in each time phase based on the difference of the movement vector in each time phase obtained by the subtraction unit 35. Assuming that the movement vector of the center of gravity is the movement vector of the whole heart movement, the influence of the whole heart movement can be removed by subtracting the movement vectors.

  The marker generation unit 37 generates a marker that represents the contour of the intima in each time phase obtained by the contour reconstruction unit 36. Furthermore, as in the first embodiment, the marker generation unit 37 assigns a different color for each time phase to each time phase marker. The display control unit 6 causes the display unit 7 to display a marker (color image) assigned with a different color for each time phase on the tomographic image of the time phase designated by the operator. Then, as in the first embodiment, the cardiac function evaluation unit 20 performs evaluation of cardiac function.

  As described above, the position of the center of gravity of the contour in each time phase is assumed to be the position of the heart's contraction center, the moving speed of the contraction center position is assumed to be equal to the speed of the whole heart motion, and the intima By subtracting the moving speed of the center of gravity from the moving speed of each point on the contour of the heart, the contour of the intima in which the influence of the whole heart motion is reduced can be obtained. Further, even when the movement vector of the center of gravity is subtracted from the movement vector of each point on the intima outline, the intima outline in which the influence of the whole heart motion is reduced can be obtained. In the range where the above assumption is established, it is possible to analyze the cardiac function while reducing the influence of the whole heart motion.

(Operation)
Next, the operation of the ultrasonic diagnostic apparatus according to the second embodiment of the present invention will be described with reference to FIGS. FIG. 5 is a flowchart showing a first operation mode of the ultrasonic diagnostic apparatus according to the second embodiment of the present invention. FIG. 6 is a flowchart showing a second operation mode of the ultrasonic diagnostic apparatus according to the second embodiment of the present invention. First, the first operation mode will be described with reference to FIG. 5, and then the second operation mode will be described with reference to FIG.

(First operation mode)
First, as in the first embodiment, by executing the processing from step S01 to step S05 shown in FIG. 3, a plurality of temporally continuous tomographic image data representing the heart is acquired, and a tomogram of a predetermined time phase is acquired. The initial contour is set so that the papillary muscles and chords are not included on the image. For example, by transmitting and receiving ultrasonic waves over one cardiac cycle or more, a plurality of tomographic image data that are temporally continuous over one cardiac cycle or more are generated.

(Step S10)
Similar to the contour position calculation unit 12 according to the first embodiment, the contour position calculation unit 31 reads from the storage unit 5 the tomographic image data B generated next to the tomographic image A in which the initial contour is set, and speckles. By performing pattern matching between two tomographic images using a pattern, a movement vector of each point on the contour of the intima is obtained. For example, the contour position calculation unit 31 obtains a movement vector of each point on the contour of the intima in each time phase included in one cardiac cycle for all tomographic image data acquired over one cardiac cycle. The contour of the intima in each time phase is detected.

(Step S11)
The contour movement speed calculation unit 32 calculates each point on the contour in each time phase based on the movement vector of each point on the contour in each time phase obtained by the contour position calculation unit 31 and the time between each time phase. The moving speed of is calculated.

(Step S12)
On the other hand, the contraction center calculation unit 33 calculates the position of the center of gravity of the intimal contour in each time phase obtained by the contour position calculation unit 31 as an example of the position of the contraction center. Further, the contraction center calculation unit 33 calculates the center of gravity movement vector in each time phase as an example of the contraction center movement vector based on the center of gravity in each time phase.

(Step S13)
The contraction center movement speed calculation unit 34 calculates the movement speed of the center of gravity in each time phase as an example of the movement speed of the contraction center based on the movement vector of the center of gravity in each time phase and the time between each time phase.

(Step S14)
Then, the subtracting unit 35 subtracts the moving speed of the center of gravity obtained in step S13 from the moving speed of each point on the contour obtained in step S11. At this time, the subtracting unit 35 subtracts the moving speeds in the same time phase to obtain a difference in moving speed in each time phase.

(Step S15)
Then, the contour reconstructing unit 36 obtains the position of the contour of the intima in each time phase by integrating the difference in moving speed in each time phase with the time between each time phase. For example, the position of the contour of the intima in each time phase included in one cardiac cycle is obtained.

(Step S07)
Then, the marker generation unit 37 generates a marker representing the contour of the intima of each time phase obtained by the contour reconstruction unit 36. Furthermore, as in the first embodiment, the marker generation unit 37 assigns a different color for each time phase to each time phase marker.

  Then, as in the first embodiment, the cardiac function is evaluated by executing the processing of step S08 and step S09 shown in FIG.

  As described above, assuming that the moving speed of the center of gravity in each time phase is equal to the speed of the whole heart movement, subtracting the moving speed of the center of gravity from the moving speed of each point on the contour, Can be obtained. As a result, it is possible to analyze the cardiac function while reducing the influence of the whole heart motion.

(Second operation mode)
First, as in the first embodiment, by executing the processing from step S01 to step S05 shown in FIG. 3, a plurality of temporally continuous tomographic image data representing the heart is acquired, and a tomogram of a predetermined time phase is acquired. The initial contour is set so that the papillary muscles and chords are not included on the image. For example, by transmitting and receiving ultrasonic waves over one cardiac cycle or more, a plurality of tomographic image data that are temporally continuous over one cardiac cycle or more are generated.

(Step S20)
Similar to the contour position calculation unit 12 according to the first embodiment, the contour position calculation unit 31 performs pattern matching between the two tomographic images using the speckle pattern, so that the intima of the intima set by the initial contour is set. The movement vector of each point on the contour is obtained. For example, the contour position calculation unit 31 obtains a movement vector of each point on the contour of the intima in each time phase included in one cardiac cycle for all tomographic image data acquired over one cardiac cycle. The contour of the intima in each time phase is detected.

(Step S21)
The contraction center calculation unit 33 calculates the position of the center of gravity of the intimal contour in each time phase determined by the contour position calculation unit 31 as an example of the position of the contraction center.

(Step S22)
Further, the contraction center calculation unit 33 calculates the center of gravity movement vector in each time phase as an example of the contraction center movement vector based on the position of the center of gravity in each time phase.

(Step S23)
The subtracting unit 35 subtracts the movement vector of the center of gravity obtained in step S22 from the movement vector of each point on the contour obtained in step S20. At this time, the subtracting unit 35 obtains a difference between the movement vectors in each time phase by subtracting the movement vectors in the same time phase.

(Step S24)
The contour reconstruction unit 36 obtains the position of the intimal contour in each time phase based on the difference of the movement vector in each time phase obtained in step S23. For example, the position of the contour of the intima in each time phase included in one cardiac cycle is obtained.

(Step S07)
Then, the marker generation unit 37 generates a marker representing the contour of the intima of each time phase obtained by the contour reconstruction unit 36. Furthermore, as in the first embodiment, the marker generation unit 37 assigns a different color for each time phase to each time phase marker.

  Then, as in the first embodiment, the cardiac function is evaluated by executing the processing of step S08 and step S09 shown in FIG.

  As described above, by subtracting the movement vector of the center of gravity from the movement vector of each point on the contour, it is possible to obtain an image in which the influence of the whole heart muscle movement is reduced. As a result, it is possible to evaluate the cardiac function while reducing the influence of the whole heart motion.

1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to a first embodiment of the present invention. It is a figure which shows the image acquired with the ultrasound diagnosing device which concerns on 1st Embodiment of this invention, and the result of cardiac function evaluation. It is a flowchart for demonstrating a series of operation | movement by the ultrasonic diagnosing device which concerns on 1st Embodiment of this invention. It is a block diagram which shows schematic structure of the ultrasonic diagnosing device which concerns on 2nd Embodiment of this invention. It is a flowchart for demonstrating the 1st operation | movement aspect by the ultrasonic diagnosing device which concerns on 2nd Embodiment of this invention. It is a flowchart for demonstrating the 2nd operation | movement aspect by the ultrasonic diagnosing device which concerns on 2nd Embodiment of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1, 1A Ultrasonic diagnostic apparatus 2 Ultrasonic probe 3 Transmission / reception part 4 Image generation part 5 Storage part 6 Display control part 7 Display part 8 Operation part 9 Control part 10, 30 Image processing part 12, 31 Contour position calculation part 11, 37 Marker generation unit 20 Cardiac function evaluation unit 32 Contour movement speed calculation unit 33 Contraction center calculation unit 34 Contraction center movement speed calculation unit 35 Subtraction unit 36 Contour reconstruction unit 100 Tomographic image 101 Color image 102 Color bar 110 Graph 120 Band graph

Claims (8)

Ultrasonic image acquisition means for acquiring a plurality of temporally continuous tomographic image data by scanning the heart of the subject with ultrasonic waves;
The specification of the contour of the intima of the heart with respect to the tomogram based on the tomogram data acquired at a predetermined time phase is received, and the inside of the tomogram based on the tomogram data acquired at each time phase other than the predetermined time phase is received. Contour position calculating means for obtaining the position of the contour of the film by pattern matching for each time phase;
Marker generating means for generating a marker representing the contour of the intima in each time phase for each time phase, and assigning a different color for each time phase to each time phase marker;
Display control means for displaying the marker of each time phase assigned with the color on a tomographic image on a display means;
An ultrasonic diagnostic apparatus comprising:   The contour position calculating means obtains a movement vector representing a displacement and a moving direction of each point on the contour of the intima for each time phase by pattern matching between two temporally continuous tomographic image data, The ultrasonic diagnostic apparatus according to claim 1, wherein the position of the contour of the intima in each time phase is obtained based on a point movement vector. A contraction center calculation means for determining, for each time phase, the position of the contraction center defined based on the contour of the intima in each time phase;
Based on the difference between the position of the contour of the intima in each time phase obtained by the contour position calculation means and the position of the contraction center in each time phase, the position of the new intimal contour is time-phased. Contour reconstructing means to be obtained for each
The marker generating means generates a new marker representing the new intimal contour for each time phase, and assigns a different color for each time phase to the new marker for each time phase,
3. The display control unit according to claim 1, wherein the display control unit causes the display unit to display a new marker of each time phase to which the color is assigned on a tomographic image. Ultrasonic diagnostic equipment. A contraction center calculation means for determining, for each time phase, the position of the contraction center defined based on the contour of the intima in each time phase;
A contraction center moving speed calculating means for obtaining a moving speed of the contraction center in each time phase based on a displacement of the position of the contraction center in each time phase;
A contour moving speed calculating means for determining a moving speed of each point on the contour in each time phase based on the displacement of the position of the contour of the intima in each time phase determined by the contour position calculating means;
The difference between the moving speed of the contraction center and the moving speed of each point on the contour is calculated for each time phase, and based on the difference, a new contour position of the intima is obtained for each time phase. And further comprising:
The marker generating means generates a new marker representing the new intimal contour for each time phase, and assigns a different color for each time phase to the new marker for each time phase,
3. The display control unit according to claim 1, wherein the display control unit causes the display unit to display a new marker of each time phase to which the color is assigned on a tomographic image. Ultrasonic diagnostic equipment. The position of the contraction center defined based on the contour of the intima in each time phase is obtained for each time phase, and the movement vector of the contraction center representing the displacement and movement direction of the position of the contraction center in each time phase is obtained. Contraction center calculation means;
A difference between the movement vector of each point on the contour of the intima obtained by the contour position calculation means and the movement vector of the contraction center is calculated for each phase, and a new intima is calculated based on the difference. Contour reconstructing means for obtaining the position of the contour for each time phase,
The marker generating means generates a new marker representing the new intimal contour for each time phase, and assigns a different color for each time phase to the new marker for each time phase,
The ultrasonic diagnostic apparatus according to claim 2, wherein the display control unit causes the display unit to display a new marker of each time phase to which the color is assigned on a tomographic image.   The area of the range surrounded by the markers of each time phase is calculated, the ratio of the area in each time phase to the area at the time of maximum expansion of the heart is obtained, and the heart function is evaluated based on the ratio The ultrasonic diagnostic apparatus according to claim 1, further comprising a function evaluation unit. A plurality of temporally continuous tomographic image data acquired by scanning the subject's heart with ultrasonic waves is received, and the inner lining of the heart with respect to the tomographic image based on the tomographic image data acquired at a predetermined time phase A contour position calculating means for receiving a contour specification of the intima in a tomographic image based on tomographic image data acquired at each time phase other than the predetermined time phase by pattern matching for each phase ,
Marker generating means for generating a marker representing the contour of the intima in each time phase for each time phase, and assigning a different color for each time phase to each time phase marker;
Display control means for displaying the marker of each time phase assigned with the color on a tomographic image on a display means;
An ultrasonic image processing apparatus comprising: On the computer,
A plurality of temporally continuous tomographic image data acquired by scanning the subject's heart with ultrasonic waves is received, and the inner lining of the heart with respect to the tomographic image based on the tomographic image data acquired at a predetermined time phase A contour position calculating function for receiving a contour specification of the intima in a tomographic image based on tomographic image data acquired at each time phase other than the predetermined time phase by pattern matching for each time phase; ,
A marker generating function for generating a marker representing the contour of the intima in each time phase for each time phase, and assigning a different color for each time phase to the marker for each time phase;
A display control function for displaying the marker of each time phase assigned with the color on a tomographic image on a display device;
An ultrasonic image processing program characterized in that is executed.

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