WO2006121031A1 - 超音波診断装置及び超音波画像表示方法 - Google Patents
超音波診断装置及び超音波画像表示方法 Download PDFInfo
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- WO2006121031A1 WO2006121031A1 PCT/JP2006/309290 JP2006309290W WO2006121031A1 WO 2006121031 A1 WO2006121031 A1 WO 2006121031A1 JP 2006309290 W JP2006309290 W JP 2006309290W WO 2006121031 A1 WO2006121031 A1 WO 2006121031A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
- A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/13—Tomography
- A61B8/14—Echo-tomography
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52023—Details of receivers
- G01S7/52036—Details of receivers using analysis of echo signal for target characterisation
- G01S7/52042—Details of receivers using analysis of echo signal for target characterisation determining elastic properties of the propagation medium or of the reflective target
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52053—Display arrangements
- G01S7/52057—Cathode ray tube displays
- G01S7/52071—Multicolour displays; using colour coding; Optimising colour or information content in displays, e.g. parametric imaging
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52053—Display arrangements
- G01S7/52057—Cathode ray tube displays
- G01S7/52073—Production of cursor lines, markers or indicia by electronic means
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52053—Display arrangements
- G01S7/52057—Cathode ray tube displays
- G01S7/52074—Composite displays, e.g. split-screen displays; Combination of multiple images or of images and alphanumeric tabular information
Definitions
- the present invention relates to an ultrasonic image display method and an ultrasonic diagnostic apparatus. Specifically, the physical quantity correlates with the distortion of the yarn and the weaving of each part of the living body with respect to the amount of compression applied to the subject.
- the present invention relates to an ultrasonic image display method and an ultrasonic diagnostic apparatus capable of providing an image to a user and improving tissue discrimination in diagnosis.
- An ultrasonic diagnostic apparatus obtains displacement of each part of a living body by applying pressure to a subject using a technique or a mechanical method, and images information on tissue hardness based on the obtained displacement. It is a device that makes it possible to properly distinguish a diseased tissue such as a cancer tumor by culling.
- a strain image which is one of the tissue hardness information, is an image obtained by spatially differentiating the displacement distribution to obtain the strain of each part of the living body and adding gradation according to the hue and brightness according to the magnitude of the strain. It is.
- strain is a qualitative physical quantity that depends on the amount of compression, and the magnitude of strain changes depending on how the compression force is applied. For this reason, even with the same yarn and weave, the amount of compression may be large, and the distortion or distortion may be displayed as a hue or brightness with a large value, which may cause misidentification due to the experience and skill of the examiner. There is.
- Patent Document 1 proposes an attempt to acquire the hardness characteristics of a tissue based on a strain image without correlating with the amount of compression.
- ROI-l and ROI-2 are set for the lesion tissue and the surrounding tissue in the strain image, respectively, and the ratio ⁇ ⁇ / ⁇ 2 of strain ⁇ 1, ⁇ 2 within each ROI is set as the hardness index. It has been suggested that This has the advantage that the relative ratio of the strain in the two regions of interest does not depend on the amount of compression, so that the difference in strain between the diseased tissue and the surrounding tissue can be identified semi-quantitatively.
- Patent Document 1 US Patent Publication WO 2006/013916
- an ultrasonic image of a lesion such as a cancer tumor is observed to determine whether the lesion tissue is benign or malignant.
- the difference in hardness identifies the boundary between the diseased tissue and the normal tissue, or if the hardness of the tissue surrounding the diseased tissue or the change in the hardness of the boundary tissue between the diseased tissue and the surrounding tissue is known It can be expected that the tissue at the lesion site can be properly identified.
- An object of the present invention is to display a spatial distribution of tissue hardness excluding the influence of the compression amount as an image.
- the ultrasonic diagnostic apparatus of the present invention is configured as follows.
- an ultrasonic probe an ultrasonic tomographic data measuring means for measuring ultrasonic tomographic data of a tomographic part by applying pressure to the tissue of the subject, and a tomographic image generation for generating a tomographic image from the ultrasonic tomographic data
- an elastic image generating means for obtaining a physical quantity that correlates with tissue distortion at a plurality of measurement points of the tomographic part based on the ultrasonic tomographic data and generating an elastic image at the tomographic part based on the physical quantity.
- means for selecting a reference area from a tomographic image or an elasticity image, and an indexed elasticity image representing the distribution of index values by converting the physical quantity of each measurement point into an index value based on the physical quantity of the reference area as a reference And means for generating.
- the ultrasonic image display method of the present invention is configured as follows. That is, a step of measuring the ultrasonic tomographic data by applying pressure to the tissue of the subject, and obtaining a physical quantity correlated with tissue distortion at a plurality of measurement points of the tomographic site of the subject based on the ultrasonic tomographic data. A step of generating an elasticity image of the tomographic site based on the physical quantity; a step of selecting a reference area for the inertial image; and the physical quantity of each measurement point based on the physical quantity of the reference area And a step of generating an indexed elasticity image representing the distribution of the index value.
- the spatial distribution of tissue hardness excluding the influence of the compression amount can be displayed as an image.
- FIG. 1 is a block configuration diagram of an embodiment of an ultrasonic diagnostic apparatus to which an ultrasonic image display method of the present invention can be applied.
- FIG. 2 is a flowchart showing a processing procedure of an embodiment of the ultrasonic image display method of the present invention.
- FIG. 3 is an external view showing an example of an ultrasonic probe.
- FIG. 4 is a diagram for explaining a problem of a conventional distorted image for explaining the effect of the embodiment of the present invention.
- FIG. 5 is a diagram showing an indexed elasticity image of an example of the present invention.
- FIG. 6 is a diagram showing an indexed elasticity image of another example of the present invention.
- FIG. 7 is a diagram for explaining an example of a method for automatically setting a reference area according to an index value of the present invention.
- FIG. 8 is a diagram for explaining another example of the reference region automatic setting method according to the index value of the present invention.
- FIG. 9 is a diagram showing an indexed elasticity image of another example of the present invention.
- FIG. 10A is a diagram for explaining a method of moving a reference region related to an index value of the present invention by following a tissue variation accompanying compression.
- FIG. 10B A specific example of the tracking processing of the points constituting the reference region R according to the index value of the present invention.
- FIG. 10C is a diagram showing a specific example of the tracking process of the reference region R according to the index value of the present invention.
- FIG. 11 is a diagram for explaining an example of gradation of the indexed elasticity image of the present invention.
- FIG. 12 is a diagram for explaining another example of gradation of the indexed elasticity image of the present invention.
- FIG. 13 is a diagram for explaining still another example of gradation conversion of the indexed elasticity image of the present invention.
- FIG. 14 is a diagram illustrating an example in which the indexed elasticity image of the present invention is displayed superimposed on a B-mode image.
- FIG. 15 is a diagram for explaining an embodiment in which a region of interest is set in the indexed elasticity image of the present invention, and an average value of hardness index values of the region of interest is numerically displayed.
- FIG. 16 is a diagram for explaining an embodiment in which an indexed elasticity image is generated as a whole by subdividing an elasticity image in the lateral direction and performing indexing for each segmented image.
- FIG. 1 is a block diagram of an ultrasonic diagnostic apparatus according to an embodiment suitable for carrying out the ultrasonic image display method of the present invention.
- FIG. 2 shows a flowchart of one embodiment of the ultrasonic image display method according to the feature of the present invention.
- the ultrasonic probe 2 used in contact with the subject 1 transmits ultrasonic waves to and from the subject 1 as shown in FIG. 3 (A).
- a plurality of receiving transducers are formed to have an ultrasonic transmission / reception surface 21 in which the transducers are aligned.
- the probe 2 is driven by ultrasonic pulses supplied from the transmission circuit 3.
- the transmission / reception control circuit 4 controls the transmission timing of the ultrasonic pulses that drive the plurality of transducers of the probe 2 so as to form an ultrasonic beam toward the focal point set in the subject 1. It has become.
- the transmission / reception control circuit 4 electronically scans the ultrasonic beam in the direction in which the transducers of the probe 2 are arranged.
- the probe 2 receives a reflected echo signal generated from within the subject 1 and outputs it to the receiving circuit 5.
- the reception circuit 5 takes in the reflected echo signal and performs reception processing such as amplification.
- the reflected echo signal received and processed by the receiving circuit 5 is amplified by adding together the phases of the reflected echo signals received by the plurality of transducers in the phasing and adding circuit 6.
- the reflected echo signal (hereinafter referred to as ultrasonic tomographic data) that has been phased and added by the phasing and adding circuit 6 is input to the signal processing unit 7 to receive signals such as gain correction, log compression, detection, contour enhancement, and filter processing. No. processing is done.
- the radio frequency (RF) signal of the ultrasonic tomographic data generated in the phasing addition circuit 6 may be a complex demodulated I and Q signal.
- the ultrasonic tomographic data processed by the signal processing unit 7 is guided to a black and white scan converter 8, where it is converted into a digital signal and converted into two-dimensional tomographic image data corresponding to the scanning plane of the ultrasonic beam. Converted.
- These signal processing unit 7 and monochrome scan converter 8 constitute a tomographic image reconstruction means.
- the tomographic image data output from the black-and-white scan converter 8 is supplied to the image display 10 via the switching adder 9 so that the tomographic image is displayed.
- the ultrasonic tomographic data output from the phasing addition circuit 6 is RF signal frame data.
- Data acquisition unit 11. The RF signal frame data acquisition unit 11 acquires a plurality of frames of RF signal groups corresponding to the scanning plane (tomographic plane) of the ultrasonic beam as frame data and stores them in a memory or the like.
- the displacement measurement unit 12 sequentially captures a plurality of pairs of frame data with different acquisition times stored in the RF signal frame data acquisition unit 11, and based on the acquired pair of frame data, displacement vectors of a plurality of measurement points on the tomographic plane. And output to the strain Z modulus calculator 13 as displacement frame data.
- the strain Z elastic modulus calculation unit 13 obtains strains at a plurality of measurement points on the tomographic plane based on the input displacement frame data, and outputs the strain to the elasticity data processing unit 14 as elasticity frame data. ing.
- the strain Z elastic modulus calculation unit 13 takes in pressure measurement data applied to the specimen from the pressure gauge side part 19 and obtains the stress distribution of each part of the subject, and obtains the strain frame data and stress distribution obtained previously.
- the elastic modulus is obtained from the above and is output to the elastic data processing unit 14 as elastic frame data.
- the elastic data processing unit 14 is a strain Z elastic modulus calculation unit 13 force input to the elastic frame data of strain or elastic modulus, smoothing processing in the coordinate plane, contrast optimization processing, and time axis direction between frames It performs various image processing such as smoothing processing and sends it to the color scan converter 15! /.
- the color scan converter 15 converts the elastic frame data output from the elastic data processing unit 14 to generate a color elastic image, and displays it on the image display 10 via the switching addition unit 9. ing.
- the color scan converter 15 has red, green, and gray scales (for example, 256 gradations) applied to an elastic image based on a range of preset upper and lower limits of elasticity (strain or elastic modulus).
- a hue code such as blue is given.
- an area where the distortion of the inertia frame data is measured is converted into a red code, and an area where the distortion is measured is converted into a blue code.
- a black and white scan converter can be used in place of the color scan converter 15. In this case, the distribution of the distortion can be expressed by brightening the brightness of the area where the distortion is greatly measured, and darkening the brightness of the area where the distortion is measured.
- the switching addition unit 9 receives black and white tomographic image data output from the black and white scan converter 8 and color elastic image data output from the color scan converter 15. , A function to switch both images and display one of them, a function to make one of both images semi-transparent, add and combine them and display them on the image display 10, and a function to display both images side by side It is formed. Further, the cine memory unit 18 stores the image data output from the switching addition unit 9 in the memory, and recalls the past image data and displays it on the image display 10 in accordance with a command from the device control interface unit 17. It is like that. In addition, the selected image data can be transferred to a recording medium such as an MO.
- the index value calculation unit 16 starts processing in accordance with the control command output from the device control interface unit 17, takes in the elastic frame data calculated by the strain Z elastic modulus calculation unit 13, and performs indexed elasticity according to the present invention.
- Image frame data is generated and output to the color scan converter 15.
- the color scan converter 15 generates a gradation indexed elasticity image based on the indexed inertial image frame data and displays it on the image display 10 via the switching addition unit 9. It is summer. Details of the index value calculation unit 16 will be described later.
- the probe 2 scans the subject 1 with an ultrasonic beam while changing the pressure in the subject 1 and continuously receives reflected echo signals from the scanning surface. Based on the ultrasonic tomographic data output from the phasing addition circuit 6, a tomographic image is reconstructed by the signal processing unit 7 and the black and white scan converter 8 and displayed on the image display 10.
- the RF signal frame data acquisition unit 11 acquires ultrasonic tomographic data in the process of changing the compression force applied to the subject 1 and repeatedly acquires frame data in synchronization with the frame rate. Save in chronological order in the built-in frame memory. Then, a plurality of pairs of frame data are successively selected and output to the displacement measuring unit 12 with a pair of frame data having different acquisition times as a unit.
- the displacement measurement unit 12 performs one-dimensional or two-dimensional correlation processing on the selected pair of frame data, and measures the displacement of each measurement point on the scanning plane to generate displacement frame data.
- a method for detecting the displacement vector for example, a block matching method or a gradient method described in JP-A-5-317313 is disclosed. It has been known.
- the image is divided into blocks consisting of, for example, NXN pixels, and the previous frame force is searched for the block closest to the target block in the current frame, and the displacement of the measurement point is obtained based on this. Also, the displacement can be calculated by calculating the autocorrelation in the same region of the pair of RF signal frame data.
- the displacement frame data obtained by the displacement measurement unit 12 is input to the strain Z elastic modulus calculation unit 13, and the distortion or elastic modulus at each measurement point is calculated to obtain elastic frame data as an elastic data processing unit 14. Is output.
- the calculation of distortion is calculated by spatially differentiating the displacement distribution as is well known.
- the elastic modulus at each measurement point is calculated based on the obtained strain.
- the measured value of the pressure measured by the pressure measuring unit 19 is taken in, and based on this, the stress at each measurement point is calculated.
- the pressure measuring unit 19 is configured by providing a reference deformable body 33 on the surface of the compression plate 31, for example, as shown in FIG.
- the strain Z coefficient calculation unit 13 calculates the stress at the measurement point inside the subject 1 based on the deformation of the reference deformable body 33. In this way, the strain Z elastic modulus calculation unit 13 calculates the elastic modulus (for example, Young's modulus) at each measurement point on the tomographic plane from the stress at each measurement point and the strain frame data obtained by the strain Z elastic modulus calculation unit 13. The ratio Ym) is calculated and output to the elastic data processing unit 14.
- the elasticity data processing unit 14 generates elasticity image data based on the strain or the elastic modulus, and displays the elasticity image on the image display 10 via the force large scan converter 15 and the switching addition unit 9.
- FIG. 2 is a flowchart showing the procedure for generating the indexed elasticity image of the first embodiment.
- a reference region R is set in a strain image 41, which is one of elastic images, and this is performed.
- FIG. 6 is an example of generating and displaying the indexed elasticity image 51 shown in FIG. 5 based on this.
- step S 1 of FIG. 2 a command is sent to the strain Z elastic modulus calculator 13 to display the strain image 41 on the image display 10.
- step S 1 of FIG. 2 a command is sent to the strain Z elastic modulus calculator 13 to display the strain image 41 on the image display 10.
- the strain Z elastic modulus calculation unit 13 takes in the strain image frame data and calculates the average strain value of the region corresponding to the reference region R as the reference strain ⁇ (S3). Then
- the index value R which is the relative ratio between the strain ⁇ and the reference strain ⁇ at each strain measurement point (i, j), is
- index is not limited to the ratio, and any index that reflects the difference between ⁇ and ⁇ may be used.
- any index that reflects the difference between ⁇ and ⁇ may be used.
- Hard measurement point R ⁇ 1
- soft measurement point R ⁇ 0
- An index that is standardized so as to take a value between 0 and 1 can be used.
- the magnitude of the strain depends on the amount of compression at that time. For example, as shown in FIG. 4 (A), it is assumed that the strain at measurement point 1 and measurement point 2 in the living body is 0.8% and the strain at measurement point 3 is 0.1% with a certain amount of compression. On the other hand, as shown in Fig. 4 (B), the strain at measurement point 1 and measurement point 2 is 1.6% and the strain at measurement point 3 is 0.2% as shown in Fig. 4 (B). is there.
- a distortion image is gradated based on the magnitude (%) of the distortion, as shown in FIG.
- the reference region R is set.
- the indexed elastic image 51 is generated by gradation!
- an indexed elasticity image 51 is obtained in which the gradation distribution such as the luminance distribution does not change, as is clear by comparing FIGS. Therefore, the image pattern of the border of the tumor part 42 at the site of interest can be recognized with high sensitivity. In particular, the difference in hardness of the boundary tissue 44 from the surrounding tissue 2 of the tumor part 42 can be identified.
- the figure shown on the right side of 05 (A) and ( ⁇ ) shows the distribution of index values on the analysis line connecting measurement points 1 and 2.
- fat is the softest tissue. If the reference region R is set in this region, the other regions are harder than fat, so
- the relative ratio which is the only index value R, has a value of 1 or more. The harder the tissue, the larger the relative ratio is.
- the reference strain can be detected with high sensitivity.
- the fat thickness varies greatly between individuals, and it may not be possible to ensure a sufficiently wide area as a reference area.
- a reference region is set in the kidney, and a ratio R to the distortion of each measurement point G, j) of the liver is calculated based on Equation (1) to generate an indexed elasticity image of the liver. It's okay.
- the adipose tissue of the prostate membrane may be used as the reference region.
- an indexed elasticity image is generated based on a strain image.
- the present invention is not limited to this, and an elasticity modulus, which is information related to tissue hardness characteristics
- An indexed elasticity image can be generated using tissue characteristic data such as viscosity, and the same effect as in this embodiment can be obtained.
- the average value of distortion in the reference region R is used as an index as the reference distortion ⁇ .
- the present invention is not limited to this, and the median value of the distortion in the reference region R and the i, j 0
- the strain value of one measurement point may be set as the reference strain ⁇ .
- the physical quantity correlated with the strain at the plurality of measurement points of the tomographic site is normalized based on the physical quantity correlated with the set strain of the reference site. It is represented as an index value image. Since the index value is a relative value of each part that receives the same amount of compression, the index value hardly changes even if the amount of compression changes. Therefore, the indexed elasticity image of the present invention eliminates the effect of the compression amount, changes the hardness from the lesion tissue to the surrounding tissue, or the difference in the hardness of the boundary region, based on the hardness of the reference region. Semi-quantitative display. As a result, it becomes easier to objectively and universally distinguish between benign and malignant lesions.
- a reference region R that is a reference region for indexing is set in a living tissue.
- the present invention is not limited to this, and when ultrasonic tomographic data is acquired using the probe 2 having the reference deformable body 33 which is an elastic member shown in FIG. 3 (B), as shown in FIG.
- the image 53 of the reference deformable body 33 is displayed in the tissue region closest to the probe 2.
- a reference area R is set in the image area of the reference deformable body 33, and the finger is designated as in the first embodiment.
- a standardized elasticity image 52 can be generated and displayed.
- the approximate elastic modulus E at each measurement point can be obtained by the following equation (2).
- force indicating the use of an external reference deformable body is not limited to this, and the reference deformable body may be disposed in the subject.
- the reference deformable body may be disposed in the subject.
- take a picture of the prostate In this case, a catheter that also inserts the base force of the foot is used as a reference deformable body. This catheter
- the outer diameter of the catheter is 1-2 mm.
- imaging is performed using a prostate probe.
- This catheter site is used as a reference deformable body.
- the balloon inserted into the body is hollow and can be expanded and contracted by inserting a liquid such as liquid rubber gel.
- the outer diameter when expanded is 0.5 to 5 mm, and the outer diameter can be arbitrarily set by adjusting the amount of liquid inserted.
- the reference region R is set to the device control interface 17 force input.
- 0 can be set automatically. For example, the softest area in a distorted image is detected, and the reference area R
- the diagram shown in Fig. 7 (A) is a B-mode tomographic image 54 of the mammary gland region, and the adipose tissue appears closest to the probe 2, and the adipose tissue is measured at the measurement site.
- the softest! / ⁇ organization the force that can detect the boundary between fat 61 and mammary gland 62 in B-mode image 54 is extracted, and the region up to the boundary with mammary gland is extracted as the reference region R.
- an index with the entire tissue 1 of fat 61 as the reference region R is used.
- a zero elasticity image 55 is obtained.
- the cursor 63 on the display screen is moved to a desired reference area by operating an input device such as a mouse, and clicked to specify.
- the same tissue region including the region is identified based on the elasticity information such as strain value and the luminance information and pattern information of the B-mode tomogram, and the reference region R is automatically set.
- the mammary gland is shown as an example, but the present invention is not limited to this, and the elasticity evaluation of the plaque 58 in the carotid artery portion 57, etc. The same applies to odor.
- the region of the muscle 59 is set as the reference region R,
- Diagnosis can be made by imaging the vascular wall 60 and plaque 58 distortion index values.
- the reference area R is always fixed and set as a fixed coordinate area.
- the reference region R is always followed by following the same tissue region.
- the distortion value can be set as the reference strain ⁇ , and the index value can be obtained accurately by eliminating disturbance.
- a coordinate system is set in which the y-coordinate is set in the horizontal direction and the X-coordinate is set in the depth direction on the ⁇ mode image, and the measurement points in the direction along the line yl
- the tissue at coordinates (xl (t-1), yl (t-1) moves to coordinates (xl (t), yl (t >>) at time t.
- the organization at the coordinates (x2 (t-1), yl (t-1) moves to the coordinates (x2 (t), yl (t >>) at time t ⁇ .
- the displacement measurement unit 12 calculates the displacement d (x, y) at all measurement points (X, y). For example, the distribution d (x (tl)) of the displacement along the line yl from the time t-1 to the time t is obtained as shown in the figure, and the X coordinate after the movement at the current time t, xl ( t) and x2 (t) are
- x2 (t) x2 (t-l) + d (x2 (t-l))
- the same tissue region can be tracked and followed.
- the tracking process may be performed with high accuracy by using information on displacement at coordinates arranged along a line indicating a boundary and based on more information.
- the displacement information at the coordinates inside the reference area R is used to follow the position with higher accuracy.
- Processing may be performed.
- the correspondence between the index value and the gradation level when gradation of the indexed elastic image based on the index value of each measurement point has not been particularly explained.
- a variety of gradation functions such as a proportional function, a logarithmic function, and a setting function with a high resolution near the threshold for judging benign or malignant tissue, are applied as the gradation function that defines the relationship between the value and the gradation level. be able to.
- the gradation function is a proportional function, for example, an 8-bit 256-level gradation map expressed by the index value, hue, and luminance.
- the linear function Can be assigned to a clerk.
- the gradation function can be defined by a logarithmic function.
- a specific part may be displayed as an index of the elastic modulus.
- the normal fat is 20 kPa, which is displayed as an index.
- Other parts are also displayed in terms of elastic modulus. Therefore, it is possible to recognize benign and malignant images with high sensitivity with respect to normal parts.
- the gradation function of a special gradation map in which the hue and luminance change greatly depending on whether it is larger or smaller than the threshold Rth. can be prepared and mapped accordingly.
- the hue and brightness of the gradation map can be changed stepwise and discontinuously in a range 77 where the index value power S of the bar display 76 is small.
- a certain colored range 79 is set near the threshold Rth of the bar display 78, for example, and the examiner moves the colored range 79 up and down by a pointing device or the like.
- the examiner can increase or decrease the threshold value Rth in real time and perform processing such as coloring only the area exceeding the threshold value Rth.
- the indexed elasticity image formed in each of the above embodiments is a B-mode image, a strain image, or the like. They can be displayed side by side or independently on the elastic image. Furthermore, for example, as shown in FIG. 14, the indexed elasticity image may be superimposed and displayed as a color translucent image on the black and white B-mode image.
- the size and position of the reference region R of the indexed elasticity image are set using the B-mode image as a guide.
- the present invention sets a region of interest ROI in the displayed indexed elasticity image, and sets the reference region R
- Analysis of tissue hardness with zero can be performed. For example, as shown in FIG. 15, by setting the region of interest ROI on the indexed elasticity image, the average value of the distortion in the ROI is obtained and displayed in association with the vicinity of the region of interest ROI, for example. . Multiple ROIs can be set.
- a B-mode image or a distorted image and an indexed elasticity image are generated and displayed in real time.
- the present invention is not limited to this, and various settings can be made offline after freezing. It is also possible to generate and display an indexed elasticity image using the elasticity frame data secured in the cine memory.
- the biological tissue of the subject 1 is uniformly compressed by the probe 2, but the probe 2 is inclined with respect to the body surface of the subject 1. If a pressing operation such as pressing in a pressed state is inappropriate, the living tissue is compressed unevenly. In particular, the pressure becomes uneven in the direction perpendicular to the transmission / reception direction (that is, the sound ray direction) (hereinafter referred to as the lateral direction). As a result, the distortion of the reference area is uneven in the lateral direction, and the index value may be inaccurate. Therefore, in this embodiment, even when the distortion of the reference region becomes nonuniform, the influence is eliminated and the index value is obtained with high accuracy. For this purpose, the entire image area is subdivided in the lateral direction so that it can be regarded as being uniformly compressed within each subdivided area. Then, index values are calculated for each subdivided area. Put out.
- FIG. 16 shows a specific example of this example.
- FIG. 16 shows an example of an indexed elasticity image displayed on the image display device 10 representing an indexed elasticity image including a reference area and other areas.
- This indexed elasticity image is subdivided into strips in the lateral direction, for example, M pieces, and a plurality of elongated subregions R 1, R 2,.
- each subdivision reference region can be, for example, about several mm. Then, an index value of distortion at each measurement point is obtained using the reference distortions ⁇ , ⁇ ,..., ⁇ ,. That is, for example, as shown in Figure 16
- the strain ⁇ measured at the measurement point G, j) is considered to have been given via the subdivision reference region R within the subdivision region. Therefore, the index value R at the measurement point (i, j) is
- the index value can be obtained for each subdivided area. As a result, the index value can be accurately obtained for the entire indexed elasticity image.
- the subdivision area is described as being relatively wide in the lateral direction.
- the subdivision area is set independently for each line, and the index value R at the measurement point G, j) is expressed by the following equation. (4), j to get it! /, Even!
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US11/913,852 US9060737B2 (en) | 2005-05-09 | 2006-05-09 | Ultrasonic diagnostic apparatus and ultrasonic image display method |
JP2007528278A JP5160227B2 (ja) | 2005-05-09 | 2006-05-09 | 超音波診断装置及び超音波画像表示方法 |
EP06746121.0A EP1880679B1 (en) | 2005-05-09 | 2006-05-09 | Ultrasonograph and ultrasonic image display method |
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JP2011505957A (ja) * | 2007-12-17 | 2011-03-03 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | 弾性イメージングにおけるひずみ利得補償の方法およびシステム |
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Also Published As
Publication number | Publication date |
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EP1880679A4 (en) | 2009-10-21 |
JPWO2006121031A1 (ja) | 2008-12-18 |
US20090216123A1 (en) | 2009-08-27 |
JP5160227B2 (ja) | 2013-03-13 |
EP1880679B1 (en) | 2015-10-07 |
US9060737B2 (en) | 2015-06-23 |
CN101160099A (zh) | 2008-04-09 |
EP1880679A1 (en) | 2008-01-23 |
CN100544678C (zh) | 2009-09-30 |
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