CN108261208B - Free M-type ultrasonic imaging system and method - Google Patents
Free M-type ultrasonic imaging system and method Download PDFInfo
- Publication number
- CN108261208B CN108261208B CN201611263816.9A CN201611263816A CN108261208B CN 108261208 B CN108261208 B CN 108261208B CN 201611263816 A CN201611263816 A CN 201611263816A CN 108261208 B CN108261208 B CN 108261208B
- Authority
- CN
- China
- Prior art keywords
- image
- motion vector
- line
- vector field
- point
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- 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
- A61B8/486—Diagnostic techniques involving arbitrary m-mode
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Biophysics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Pathology (AREA)
- Radiology & Medical Imaging (AREA)
- Biomedical Technology (AREA)
- Veterinary Medicine (AREA)
- Medical Informatics (AREA)
- Physics & Mathematics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Ultra Sonic Daignosis Equipment (AREA)
- Image Analysis (AREA)
Abstract
The invention relates to a free M-type ultrasonic imaging system and a method, which comprises the following steps: s1: b-type images are obtained through ultrasonic signal processing; s2: screening the B-type image to capture an ultrasonic B-type image frame corresponding to the user-defined sampling line selected by the user, and generating M-type line data from polar coordinate data of the B-type image user-defined sampling line; s3: interpolating each point coordinate corresponding to the M-shaped line data according to the endpoint coordinate of the custom sampling line on the current frame image; s4: interpolating forward and backward motion vector fields according to coordinates of all points on a plurality of M-shaped lines corresponding to the previous frame of image; s5: performing compensation processing on the forward and backward motion vector fields after removing the abnormal value and smoothing; s6: and carrying out bilinear interpolation on the compensated forward and backward motion vector fields to interpolate the length of the M-shaped line. The invention can obtain the free M-shaped ultrasonic image more efficiently, and can set various parameters of the free M-shaped ultrasonic imaging according to the requirements of users.
Description
Technical Field
The invention relates to a free M-shaped ultrasonic imaging system and a free M-shaped ultrasonic imaging method, and belongs to the technical field of ultrasonic imaging systems and methods.
Background
The free M-mode imaging technology is a relatively new technology in the existing ultrasound imaging, the conventional M-mode imaging is based on a real ultrasound scanning line, the free M-mode imaging is based on a self-defined virtual straight line or curve of a two-dimensional ultrasound image, and the free M-mode imaging is essentially another expression form of a two-dimensional ultrasound image sequence. Conventional ultrasound B-mode imaging can provide more complete spatial information, but clinically M-mode imaging is more accurate in assessing cardiac chamber size and cardiac function. In the existing conventional M-mode ultrasound, some are suitable for high-frequency equipment, some are suitable for low-frequency equipment, and a free M-mode ultrasound imaging system and method suitable for a wider probe frequency range are needed to be invented, so that the system can obtain a free M-mode ultrasound image more efficiently, and various parameters of the free M-mode ultrasound imaging can be set according to the requirements of a user.
Disclosure of Invention
The invention aims to overcome the defects in the prior art and provide a free M-mode ultrasonic imaging system and a free M-mode ultrasonic imaging method, which can obtain a free M-mode ultrasonic image more efficiently and can set various parameters of the free M-mode ultrasonic imaging according to the requirements of a user.
According to the technical scheme provided by the invention, the free M-type ultrasonic imaging system is characterized by comprising:
A probe for transmitting/receiving an ultrasonic signal;
The digital signal processing module is connected with the probe and is used for receiving the ultrasonic signals and processing the ultrasonic signals to obtain digital signals;
The digital scanning conversion module is connected with the digital signal processing module and is used for processing the digital signal to obtain a B-type image;
The free M processing module is connected with the digital scanning conversion module;
The display is connected with the digital scanning conversion module and the free M processing module;
The free M processing module includes:
The image screening processing module is used for screening a B-type image to capture an ultrasonic B-type image frame corresponding to a custom sampling line selected by a user, simultaneously recording the time for capturing the ultrasonic B-type image frame, adjustably placing the B-type image at a proper position of a display according to the proportion required by the user, and simultaneously generating the polar coordinate data of the obtained B-type image custom sampling line into M-type line data;
The interpolation processing module interpolates the coordinates of each point of the custom sampling line corresponding to the M-shaped line data according to the endpoint coordinates of the custom sampling line selected on the current frame image; interpolating a forward motion vector field and a backward motion vector field according to coordinates of all points on a plurality of M-shaped lines corresponding to the previous frame of image;
The filtering module is used for removing abnormal values according to the forward motion vector field, the backward motion vector field and a preset threshold value and then smoothing all the calculated forward point sets and backward point sets;
The interpolation rear-end module is used for performing compensation processing on the forward motion vector field and the backward motion vector field after removing the abnormal value and smoothing, performing bilinear interpolation on the compensated forward motion vector field and backward motion vector field, and interpolating the length of the M-shaped line; and displaying the obtained M-shaped line in a self-defined area of the display according to the proportion set by a user.
The free M-type ultrasonic imaging method is characterized by comprising the following steps:
S1: a user selects a proper probe according to needs, the probe transmits/receives ultrasonic signals, the digital signal processing module receives the signals and processes the signals to obtain digital signals, and the digital scanning conversion module processes the digital signals to obtain a B-type image;
S2: the image screening processing module screens the B-type image to capture an ultrasonic B-type image frame corresponding to the user-defined sampling line selected by the user, and simultaneously records the time for capturing the ultrasonic B-type image frame; the B-type image is adjustably placed at a proper position of a display according to the proportion required by a user, and meanwhile, the obtained polar coordinate data of the B-type image custom sampling line is generated into M-type line data;
S3: the interpolation processing module interpolates the coordinates of each point of the custom sampling line corresponding to the M-shaped line data according to the endpoint coordinates of the custom sampling line selected on the current frame image;
S4: the interpolation processing module interpolates a forward motion vector field and a backward motion vector field according to the coordinates of all points on a plurality of corresponding M-shaped lines on the previous frame of image;
S5: the interpolation rear-end module carries out compensation processing on the forward motion vector field and the backward motion vector field after removing the abnormal value and smoothing;
S6: and the interpolation rear-end module performs bilinear interpolation on the compensated forward motion vector field and the compensated backward motion vector field to interpolate the length of the M-shaped line, and displays the obtained M-shaped line in a user-defined area of the display according to the proportion set by a user.
Further, in the step S3, two end points P according to any one M-type line 1(x1,y1) And the end point P 2(x2,y2) Interpolating all points and coordinates thereof on the M-shaped line; an arbitrary point P (x, y) is located at an end point P 1(x1,y1) And the end point P 2(x2,y2) On the connection line of (2), then: (x, y) ═ x 1,y1)×(1-k)+(x2,y2) × k, wherein k is more than or equal to 0 and less than or equal to 1.
Further, the formula (x, y) ═ x 1,y1)×(1-k)+(x2,y2) in the x k, the ratio is, 
Dist is not less than 0 and not more than Dist, Dist, from endpoint P 1(x1,y1) To the end point P 2(x2,y2) Increasing the integer from 0 to Dist, wherein Dist is the length of the M-shaped line, and is max (| x) 1-x2|,|y1-y2|)。
Further, in step S4, the forward motion vector field is F (x, y) ═ P t0,(x',y')-Pt0(x, y) wherein P t0Coordinates, P, of all points of several M lines on the previous frame image t0The coordinates of each point on the current frame image are obtained;
The backward motion vector field is B (x, y) ═ P t1,(x',y')-Pt1(x, y) wherein P t1Coordinates, P, of all points of several M lines on the current frame image t1The coordinates of each point on the previous frame image.
Further, the process of removing the abnormal value in step S5 is as follows:
According to any point P on any M line 0(x0,y0) What is needed is At two end points P of the M line 1、P2solving a linear equation ax + by + c of a straight line L where the M line is located to be 0;
P on previous frame image 0The coordinate of the point on the current frame image is P t0,(x0-F,y0-F)＝F(x0,y0)+Pt0(x0,y0) P on the current frame picture 0The coordinate of the point on the previous frame image is P t1,(x0-B,y0-B)＝Pt1(x0,y0)+B(x0,y0)；
According to the formula 
Finding P t0distance between the point and the straight line L, if the distance is greater than the set threshold value, that is Dist _ F >Dist _ Threshold, then let P t0,＝P0；
According to the formula 
Finding P t1distance between point and straight line L, Dist _ B if the distance is greater than the threshold set by the operator >Dist _ Threshold, then let P t1,＝P0。
Further, the compensation processing method in step S5 is as follows: outputting M-type image for several times in the time interval between any previous frame image and current frame image, t 0+ Δ t is the moment of outputting M-type image once, Δ t is more than or equal to 0 and less than or equal to 1, then t 0the forward motion vector field and the backward motion vector field of the image at time + Δ t are denoted by F (Δ t) ═ 1- Δ t × F and B (Δ t) ═ Δ t × B, respectively.
Further, the bilinear interpolation process in step S6:
If there is no displacement between the current frame image and the current frame image, t 0the + Δ t frame image is expressed by the formula I (x, y, t + Δ t) ═ I (x, y, t) × (1- Δ t) + I (x, y, t +1) × Δ t;
When a motion vector field exists between the current frame image and the current frame image, t is determined 0+ Δ t frame map Like the following formula:
I(x,y,t+Δt)＝I(x+Bx(Δt),y+By(Δt),t)×(1-Δt)+I(x+Fx(1-Δt),y+Fy(1-Δt),t+1)×Δt。
Further, in the ultrasound imaging process, the input image is reduced by half per frame.
Further, in the ultrasonic imaging process, the minimum abscissa x _ min, the maximum abscissa x _ max, the minimum ordinate y _ min and the maximum abscissa y _ max of all M-line end coordinates set by an operator are taken out, and a region of interest is constructed by the coordinates) to narrow the effective range of the image.
The free M-shaped ultrasonic imaging system and the free M-shaped ultrasonic imaging method are suitable for free M-shaped ultrasonic imaging with a wide probe frequency range, can obtain a free M-shaped ultrasonic image more efficiently, and can set various parameters of the free M-shaped ultrasonic imaging according to the requirements of users.
Drawings
Fig. 1 is a schematic diagram of a free M-mode ultrasound imaging system according to the present invention.
Description of reference numerals: the system comprises a probe 1, a digital signal processing module 2, a digital scanning conversion module 3, a free M processing module 4, an image screening processing module 41, an interpolation processing module 42, a filtering module 43, an interpolation rear-end module 44 and a display 5.
Detailed Description
The invention is further described below with reference to the accompanying drawings.
As shown in fig. 1, the free M-mode ultrasonic imaging system of the present invention includes a probe 1, a digital signal processing module 2, a digital scan conversion module 3, a free M processing module 4 and a display 5, wherein the probe 1 is connected to the digital signal processing module 2, the digital signal processing module 2 is connected to the digital scan conversion module 3, the digital scan conversion module 3 is connected to the free M processing module 4 and the display 5, and the free M processing module 4 is connected to the display; the free M processing module 4 includes an image screening processing module 41, an interpolation processing module 42, a filtering module 43, and an interpolation back-end module 44, where the image screening processing module 41 is connected to the interpolation processing module 42, the interpolation processing module 42 is connected to the filtering module 43, and the filtering module 43 is connected to the interpolation back-end module 44.
The probe 1 is selected according to the needs of a user, and the probe 1 is used for transmitting/receiving ultrasonic signals.
The digital signal processing module 2 receives the ultrasonic signal and processes the ultrasonic signal to obtain a digital signal.
And the digital scanning conversion module 3 processes the obtained digital signal to obtain a B-type image.
The image screening processing module 41 screens the B-type image to capture an ultrasonic B-type image frame corresponding to the custom sampling line selected by the user, simultaneously records the time t for capturing the ultrasonic B-type image frame, adjustably places the B-type image at a proper position of the display according to the proportion required by the user, and simultaneously generates M-type line data from the obtained polar coordinate data of the custom sampling line of the B-type image;
The interpolation processing module 42 interpolates the coordinates of each point of the custom sampling line corresponding to the M-type line data according to the endpoint coordinates of the custom sampling line selected on the current frame image; the interpolation processing module 42 interpolates a forward motion vector field and a backward motion vector field according to the coordinates of all points on a plurality of corresponding M-type lines on the previous frame of image;
The filtering module 43 removes abnormal values according to the calculated forward motion vector field and backward motion vector field and a preset threshold, and then performs smoothing processing on all the calculated forward point set and backward point set;
The interpolation back-end module 44 performs compensation processing on the forward motion vector field and the backward motion vector field after removing the abnormal value and smoothing; the interpolation rear-end module 44 performs bilinear interpolation on the compensated forward motion vector field and backward motion vector field to interpolate the length of the M-shaped line; and the interpolation rear end module displays the obtained M-shaped line in a user-defined area of the display according to the proportion set by a user.
The invention relates to a free M-type ultrasonic imaging method, which comprises the following specific steps:
S1: the user selects a proper probe according to the requirement, the probe transmits/receives ultrasonic signals, the digital signal processing module receives the signals and processes the signals to obtain digital signals, and the digital scanning conversion module processes the digital signals to obtain B-type images.
S2: the image screening processing module screens the B-type image to capture an ultrasonic B-type image frame corresponding to the custom sampling line selected by the user, simultaneously records the time t for capturing the ultrasonic B-type image frame, adjustably places the B-type image at a proper position of a display according to the proportion required by the user, and simultaneously generates M-type line data from the obtained polar coordinate data of the custom sampling line of the B-type image; for example: the current frame image time is t 1The previous frame image is t 0If the interval between two frames is t ═ t 1-t0。
S3: the interpolation processing module interpolates the coordinates of each point of the custom sampling line corresponding to the M-shaped line data according to the endpoint coordinates of the custom sampling line selected on the current frame image;
Two end points P according to any one M type line 1(x1,y1) And the end point P 2(x2,y2) Interpolating all points and coordinates thereof on the M-shaped line; an arbitrary point P (x, y) is located at an end point P 1(x1,y1) And the end point P 2(x2,y2) Can be expressed as: (x, y) ═ x 1,y1)×(1-k)+(x2,y2) xk, wherein k is more than or equal to 0 and less than or equal to 1;
According to the formula Dist ═ max (| x) 1-x2|,|y1-y2|) the length of the M profile line; order to 
Dist 0 ≦ Dist, Dist, accompanied by a slave endpoint P 1(x1,y1) To the end point P 2(x2,y2) And increments from 0 to Dist; using the formula (x, y) ═ x 1,y1)×(1-k)+(x2,y2) and x k, interpolating the coordinates of each point on the M-shaped line.
The method has the advantages that two points can be appointed to be connected into the M-shaped line at any position of the ultrasonic image without being limited by polar coordinate conversion, so that an operator can set the M-shaped line more intuitively.
S4: the interpolation processing module is according to t 0Interpolating the coordinates of all points on a plurality of corresponding M-shaped lines on the frame image to obtain a forward motion vector field and a backward motion vector field;
Take out t 0Coordinates P of all points of several M lines on the frame image t0Using a motion tracking method (in another embodiment using a sparse optical flow algorithm) to find each point at t 1Coordinates P on the frame image t0Then, the difference F (x, y) is found to be P t0,(x',y')-Pt0(x, y), which is called the forward motion vector field; wherein F (x) ═ P t0,(x')-Pt0(x)，F(y)＝Pt0,(y')-Pt0(y) is carried out. Take out t 1Coordinates P of all points of several M lines on the frame image t1Using a motion tracking method (in another embodiment using a sparse optical flow algorithm) to find each point at t 0Coordinates P on the frame image t1And the difference B (x, y) is P t1,(x',y')-Pt1(x, y), which is called backward motion vector field; wherein B (x) ═ P t1,(x')-Pt1(x)，B(y)＝Pt1,(y')-Pt1(y)。
For the obtained forward motion vector field and backward motion vector field, the filtering module removes abnormal values in the forward motion vector field and the backward motion vector field by using the following method. For any point P on any M line 0(x0,y0) According to the two end points P of the M line where the point is located 1、P2the linear equation ax + by + c of the straight line L where the M line is located is solved to be 0. t 0P on frame image 0Point is at t 1Coordinate on frame image is P t0,(x0-F,y0-F)＝F(x0,y0)+Pt0(x0,y0)，t1P on frame image 0Point is at t 0Coordinate on frame image is P t1,(x0-B,y0-B)＝Pt1(x0,y0)+B(x0,y0). According to the formula 
Finding P t0distance between point and straight line L, Dist _ F if the distance is greater than the threshold set by the operator >Dist _ Threshold, then let P t0,＝P0. Also according to the formula 
Finding P t1distance between point and straight line L, Dist _ B if the distance is greater than the threshold set by the operator >Dist _ Threshold, then let P t1,＝P0。
After removing abnormal values, respectively comparing all P t0Forward set of points, composed of points and all P t1And smoothing the backward point set formed by the points.
In one embodiment, the input image is reduced by half per frame to increase processing speed.
In one embodiment, the minimum abscissa x _ min, the maximum abscissa x _ max, the minimum ordinate y _ min, and the maximum abscissa y _ max of all M-line endpoint coordinates set by the operator are taken, and the effective range of the image is further reduced by means of a region of interest (ROI) constructed by the minimum abscissa x _ min, the maximum abscissa y _ max, and the minimum ordinate y _ min, and the maximum abscissa y _ max, so as to improve the processing speed.
S5: and the interpolation rear-end module performs compensation processing on the forward motion vector field and the backward motion vector field after removing the abnormal value and smoothing. After removing abnormal values and smoothing processing operation, updated and more reasonable forward motion vector field F (x, y) and backward motion vector field B (x, y) are obtained.
And carrying out motion compensation calculation on the forward transport vector field and the backward motion vector field: at any time t, according to step S2 0Frame image and t 1The M-mode image needs to be output several times within the time interval t + σ t between the frame images, assuming that the M-mode image is output at a constant speed. Let Δ t be 0 or more and 1 or less, and t 0+ Δ t is exactly when the M-mode image is output once, then t 0the forward motion vector field and the backward motion vector field of the image at the time + Δ t can be represented by F (Δ t) ═ 1- Δ t × F and B (Δ t) ═ Δ t × B, respectively.
S6: and the interpolation rear-end module performs bilinear interpolation on the compensated forward motion vector field and the compensated backward motion vector field to interpolate the length of the M-shaped line, and displays the obtained M-shaped line in a user-defined area of the display according to the proportion set by a user.
Let t 0Frame image and t 1Without any displacement between the frame images, t 0the + Δ t frame image may be expressed using a bilinear difference method, i.e., using the following formula, I (x, y, t + Δ t) ═ I (x, y, t) × (1- Δ t) + I (x, y, t +1) × Δ t;
When t is 0Frame image and t 1When the motion vector field between frame images cannot be ignored, t needs to be set 0The forward motion vector field and the backward motion vector field of the image at time + Δ t are substituted into the previous formula to obtain the following formula: i (x, y, t + Δ t) ═ I (x + B) x(Δt),y+By(Δt),t)×(1-Δt)+I(x+Fx(1-Δt),y+Fy(1-Δt),t+1)×Δt。
And scaling the length of the interpolated M type line to an output specified length. According to the setting of an operator, the length can be equal to the original length of the M line; or the M-shaped images of a plurality of M-shaped lines are equal in length, and the total length of all the M-shaped images is halved. According to the requirements of users, the images are displayed in various scales and placed in proper areas and positions.
In the present invention, different preset coefficients of the scanning speed of the M-type image may be set, that is, the higher the preset coefficient is, the higher the linear velocity of the output M-type image per second is.
Claims (9)
1. A free M-mode ultrasound imaging system, comprising:
A probe (1) for transmitting/receiving an ultrasound signal;
The digital signal processing module (2), the digital signal processing module (2) is connected with the probe (1), and the digital signal processing module (2) is used for receiving the ultrasonic signals and processing the ultrasonic signals to obtain digital signals;
The digital scanning conversion module (3), the digital scanning conversion module (3) is connected with the digital signal processing module (2), and the digital scanning conversion module (3) is used for processing the digital signal to obtain a B-type image;
The free M processing module (4), the free M processing module (4) is connected with the digital scan conversion module (3);
And a display (5), wherein the display (5) is connected with the digital scan conversion module (3) and the free M processing module (4);
The free M processing module (4) comprises:
The image screening processing module (41) is used for screening a B-type image to capture an ultrasonic B-type image frame corresponding to a custom sampling line selected by a user, simultaneously recording the time for capturing the ultrasonic B-type image frame, adjustably placing the B-type image at a proper position of a display according to the proportion required by the user, and simultaneously generating M-type line data from the polar coordinate data of the obtained B-type image custom sampling line;
The interpolation processing module (42), the interpolation processing module (42) interpolates the coordinate of each point of the self-defined sampling line corresponding to the M type line data according to the endpoint coordinate of the self-defined sampling line selected on the current frame image; interpolating a forward motion vector field and a backward motion vector field according to coordinates of all points on a plurality of M-shaped lines corresponding to the previous frame of image;
The filtering module (43), after removing the abnormal value according to the forward motion vector field, the backward motion vector field and the preset threshold, the filtering module (43) carries out smoothing treatment on all the calculated forward point sets and backward point sets;
The interpolation rear-end module (44) is used for performing compensation processing on the forward motion vector field and the backward motion vector field after removing the abnormal values and smoothing, performing bilinear interpolation on the compensated forward motion vector field and backward motion vector field, and interpolating the length of the M-shaped line; displaying the obtained M-shaped line in a self-defined area of a display according to a proportion set by a user;
Wherein the process of removing the abnormal value in the interpolation back-end module (44) is as follows:
According to any point P on any M line 0(x0,y0) Two end points P of the M line 1、P2solving a linear equation ax + by + c of a straight line L where the M line is located to be 0;
P on previous frame image 0The coordinate of the point on the current frame image is P t0’(x0-F,y0-F)＝F(x0,y0)+Pt0(x0,y0) P on the current frame picture 0The coordinate of the point on the previous frame image is P t1’(x0-B,y0-B)＝Pt1(x0,y0)+B(x0,y0)；
According to the formula 
Finding P t0' Point to straight line L, if the distance is greater than a set threshold, Dist _ F >Dist _ Threshold, then let P t0’＝P0；
According to the formula 
Finding P t1' Point to straight line L, if the distance is greater than an operator-set threshold, Dist _ B >Dist _ Threshold, then let P t1’＝P0。
2. A free M-type ultrasonic imaging method is characterized by comprising the following steps:
S1: a user selects a proper probe according to needs, the probe transmits/receives ultrasonic signals, the digital signal processing module receives the signals and processes the signals to obtain digital signals, and the digital scanning conversion module processes the digital signals to obtain a B-type image;
S2: the image screening processing module screens the B-type image to capture an ultrasonic B-type image frame corresponding to the user-defined sampling line selected by the user, and simultaneously records the time for capturing the ultrasonic B-type image frame; the B-type image is adjustably placed at a proper position of a display according to the proportion required by a user, and meanwhile, the obtained polar coordinate data of the B-type image custom sampling line is generated into M-type line data;
S3: the interpolation processing module interpolates the coordinates of each point of the custom sampling line corresponding to the M-shaped line data according to the endpoint coordinates of the custom sampling line selected on the current frame image;
S4: the interpolation processing module interpolates a forward motion vector field and a backward motion vector field according to the coordinates of all points on a plurality of corresponding M-shaped lines on the previous frame of image;
S5: the interpolation rear-end module carries out compensation processing on the forward motion vector field and the backward motion vector field after removing the abnormal value and smoothing;
S6: the interpolation rear end module performs bilinear interpolation on the compensated forward motion vector field and the compensated backward motion vector field to interpolate the length of the M molded lines, and displays the obtained M molded lines in a user-defined area of the display according to the proportion set by a user;
Wherein, the process of removing the abnormal value in step S5 is as follows:
According to any point P on any M line 0(x0,y0) Two end points P of the M line 1、P2solving a linear equation ax + by + c of a straight line L where the M line is located to be 0;
P on previous frame image 0The coordinate of the point on the current frame image is P t0’(x0-F,y0-F)＝F(x0,y0)+Pt0(x0,y0) P on the current frame picture 0The coordinate of the point on the previous frame image is P t1’(x0-B,y0-B)＝Pt1(x0,y0)+B(x0,y0)；
According to the formula 
Finding P t0' Point to straight line L, if the distance is greater than a set threshold, Dist _ F >Dist _ Threshold, then let P t0’＝P0；
According to the formula 
Finding P t1' Point to straight line L, if the distance is greater than an operator-set threshold, Dist _ B >Dist _ Threshold, then let P t1’＝P0。
3. The free M-mode ultrasound imaging method of claim 2, wherein: in the step S3, two end points P according to any one M-type line 1(x1,y1) And the end point P 2(x2,y2) Interpolating all points and coordinates thereof on the M-shaped line; an arbitrary point P (x, y) is located at an end point P 1(x1,y1) And the end point P 2(x2,y2) On the connection line of (2), then: (x, y) ═ x 1,y1)×(1-k)+(x2,y2) × k, wherein k is more than or equal to 0 and less than or equal to 1.
4. The free M-mode ultrasound imaging method of claim 3, wherein: the formula (x, y) ═ x 1,y1)×(1-k)+(x2,y2) in the x k, the ratio is, 
Dist ' is not less than 0 and not more than Dist ', and Dist ' is from end point P 1(x1,y1) To the end point P 2(x2,y2) Increasing the integer from 0 to Dist, wherein Dist is the length of the M-shaped line, and is max (| x) 1-x2|,|y1-y2|)。
5. The free M-mode ultrasound imaging method of claim 2, wherein: the forward motion vector field in step S4 is F (x, y) ═ P t0’(x',y')-Pt0(x, y) wherein P t0Coordinates, P, of all points of several M lines on the previous frame image t0' is the coordinate of each point on the current frame image;
The backward motion vector field is B (x, y) ═ P t1’(x',y')-Pt1(x, y) wherein P t1Coordinates, P, of all points of several M lines on the current frame image t1' is the coordinate of each point on the previous frame image.
6. The free M-mode ultrasound imaging method of claim 2, wherein: the compensation processing method in step S5 includes: outputting M-type image for several times in the time interval between any previous frame image and current frame image, t 0+ Δ t is the moment of outputting M-type image once, Δ t is more than or equal to 0 and less than or equal to 1, then t 0the forward motion vector field and the backward motion vector field of the image at time + Δ t are denoted by F (Δ t) ═ 1- Δ t × F and B (Δ t) ═ Δ t × B, respectively.
7. The free M-mode ultrasound imaging method of claim 6, wherein: the bilinear interpolation process in step S6:
If there is no displacement between the current frame image and the current frame image, t 0the + Δ t frame image is expressed by the formula I (x, y, t + Δ t) ═ I (x, y, t) × (1- Δ t) + I (x, y, t +1) × Δ t;
When a motion vector field exists between the current frame image and the current frame image, t is determined 0The + Δ t frame image is expressed by the following equation:
I(x,y,t+Δt)＝I(x+Bx(Δt),y+By(Δt),t)×(1-Δt)+I(x+Fx(1-Δt),y+Fy(1-Δt),t+1)×Δt。
8. The free M-mode ultrasound imaging method of claim 2, wherein: in ultrasound imaging, the input image is reduced by half per frame.
9. The free M-mode ultrasound imaging method of claim 2, wherein: in the ultrasonic imaging process, extracting the minimum abscissa x _ min, the maximum abscissa x _ max, the minimum ordinate y _ min and the maximum abscissa y _ max of all M-line end point coordinates set by an operator, and constructing an interested area by the coordinates) to narrow the effective range of the image.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201611263816.9A CN108261208B (en) | 2016-12-30 | 2016-12-30 | Free M-type ultrasonic imaging system and method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201611263816.9A CN108261208B (en) | 2016-12-30 | 2016-12-30 | Free M-type ultrasonic imaging system and method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN108261208A CN108261208A (en) | 2018-07-10 |
| CN108261208B true CN108261208B (en) | 2020-08-07 |
Family
ID=62755200
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201611263816.9A Active CN108261208B (en) | 2016-12-30 | 2016-12-30 | Free M-type ultrasonic imaging system and method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN108261208B (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP7472691B2 (en) * | 2020-07-09 | 2024-04-23 | コニカミノルタ株式会社 | Ultrasound diagnostic device and ultrasonic signal processing method |
| CN114647765A (en) * | 2022-05-19 | 2022-06-21 | 支付宝(杭州)信息技术有限公司 | Graph data sampling method and system |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1923144A (en) * | 2005-08-29 | 2007-03-07 | 深圳迈瑞生物医疗电子股份有限公司 | Anatomy M shape imaging method and apparatus based on sport interpolation |
| CN103230283A (en) * | 2013-04-16 | 2013-08-07 | 清华大学 | Method for optimizing ultrasonic probe imaging plane space position calibration |
| WO2016149862A1 (en) * | 2015-03-20 | 2016-09-29 | Ge医疗系统环球技术有限公司 | Method and device for measurements on m-mode ultrasonic image |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4202697B2 (en) * | 2002-08-12 | 2008-12-24 | 株式会社東芝 | Ultrasonic diagnostic apparatus, ultrasonic image display apparatus, and ultrasonic image display method |
-
2016
- 2016-12-30 CN CN201611263816.9A patent/CN108261208B/en active Active
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1923144A (en) * | 2005-08-29 | 2007-03-07 | 深圳迈瑞生物医疗电子股份有限公司 | Anatomy M shape imaging method and apparatus based on sport interpolation |
| CN103230283A (en) * | 2013-04-16 | 2013-08-07 | 清华大学 | Method for optimizing ultrasonic probe imaging plane space position calibration |
| WO2016149862A1 (en) * | 2015-03-20 | 2016-09-29 | Ge医疗系统环球技术有限公司 | Method and device for measurements on m-mode ultrasonic image |
Also Published As
| Publication number | Publication date |
|---|---|
| CN108261208A (en) | 2018-07-10 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| EP2157800B1 (en) | Method and apparatus for increasing the frame rate of a video signal | |
| JP6282942B2 (en) | Ultrasonic diagnostic apparatus, image processing apparatus, and image processing program | |
| JP2003325519A (en) | Three-dimensional ultrasonic video forming apparatus using lateral distance correlation function | |
| CN102724398B (en) | Image data providing method, combination method thereof, and presentation method thereof | |
| US10722217B2 (en) | Ultrasonic diagnostic apparatus and medical image processing apparatus | |
| CN103903222A (en) | Three-dimensional sensing method and three-dimensional sensing device | |
| JP2011062524A (en) | Ultrasonic system and method for measuring three-dimensional distance | |
| JP6227926B2 (en) | Ultrasound imaging system | |
| CN108261208B (en) | Free M-type ultrasonic imaging system and method | |
| JP2011120881A (en) | Ultrasound system and method for providing three-dimensional ultrasound image based on sub region of interest | |
| JP2011152416A (en) | Ultrasonic system and method for processing three-dimensional ultrasonic screen image and measuring size of concerned object | |
| JP2011143250A (en) | Ultrasound system and method for setting scan angle, scan depth and scan speed | |
| Wasih et al. | Motion tracking of carotid artery in ultrasound images using Lucas Kanade method with advanced Siamese Neural Networks | |
| JP2008006283A (en) | Display apparatus and method of ultrasonic image | |
| CN113362467B (en) | Point cloud preprocessing and ShuffleNet-based mobile terminal three-dimensional pose estimation method | |
| JP2008237912A (en) | System and method for forming ultrasonic elastic image | |
| KR101121267B1 (en) | Ultrasound system and method for providing compound image considering steering angle | |
| US8157735B2 (en) | Ultrasound system and method of providing ultrasound images | |
| KR20080060625A (en) | Ultrasound diagnostic system and method for acquiring ultrasound images based on motion of a target object | |
| JP5937254B1 (en) | Ultrasonic diagnostic equipment | |
| JP6518130B2 (en) | Ultrasonic diagnostic equipment | |
| JP2020018845A (en) | Ultrasonic diagnostic apparatus and control program | |
| KR101300646B1 (en) | Apparatus and method for processing a 3-dimensional ultrasound image | |
| CN115937291A (en) | Binocular image generation method and device, electronic equipment and storage medium | |
| JP5665304B2 (en) | Ultrasonic system and method for providing volume information of a periodically moving object |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |