CN100475151C - Anatomy M shape imaging method and apparatus by using ultrasonic B shape imaging data - Google Patents
Anatomy M shape imaging method and apparatus by using ultrasonic B shape imaging data Download PDFInfo
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Abstract
The invention relates to a method for using Ultrasonic B image data to obtain dissect M-type image, and relative device. Wherein, said device comprises main controller, detector, wave combiner, checker, data buffer, and the image processing display module formed by MDSC module, interpolation module, M image buffer, BDSC module and B image buffer. The main controller controls the detector to emit and receive ultrasonic wave via inter-row scanning method, to obtain at least one group of continuous M-type data at time from one frame of B-type data with high spatial resolution; the MDSC module extracts data from scanning line buffer to be transformed into grid point data of dissect M-type; said grid point via interpolation module can improve its time resolution to meet the demand of dissect M-type image display. The invention can obtain higher dissect M-type frame rate without changing B image frame rate, to realize dissect M-type image on low-level Ultrasonic B machine.
Description
Technical field
The present invention relates to the formation method and the device of medical supersonic wave technology, thereby relate in particular to the method and apparatus that the temporal resolution that improves M type sampled data on the ultrasonic device of low frame per second under the prerequisite that does not reduce the B frame per second obtains real-time anatomy M shape image.
Background technology
Anatomy M shape (anatomical M-mode) or arbitrarily M type (arbitrary M-mode) imaging be a kind of newer technology in the ultra sonic imaging, propose in 1996 by the Vingmed sound company of Norway (the said firm in 1998 by GE corporate buyout) the earliest.Anatomy M shape imaging and conventional M type imaging manifestation mode are very similar, all are the intensity of expressing ultrasound echo signal on time and depth plane with gray scale.But from image-forming mechanism, the two difference is bigger.The imaging of conventional M type is based on a real ultrasonic scanning line, and anatomy M shape imaging is virtual M type (virtual M mode) based on self-defining straight line on the two-dimensional ultrasonic image sequence or a curve.Anatomy M shape imaging is another expression-form of two-dimensional ultrasonic image sequence in essence, arranges the view data that obtains the distance same with conventional M type-time coordinate system according to time sequencing by the sample line position data that obtains from each frame B figure.
Although the ultrasonic B imaging can provide more complete spatial information, it is more accurate to adopt the imaging of conventional M type to carry out chambers of the heart evaluation big or small and cardiac function clinically.Reason has four: the imaging of conventional M type has higher temporal resolution than Type B imaging; Heart movement can be accurately observed in the imaging of conventional M type on time shaft, and heart movement change in time can not be accurately observed in the Type B imaging; The M pattern can better be confirmed organizational boundary; The M pattern can the relatively motion of different anatomical structures on than high time resolution.Conventional M type imaging also has its deficiency.At first, in order accurately to measure the relevant parameter of ventricle, scanning line need be vertical with ventricle wall.Because the influence of lung and rib, this clinically tangent plane are not easy to obtain.Secondly, conventional M type image scanning line is fixed, heart movement can make the scanning line basic point might towards or away from the scanning fixed point, cause measuring inaccurate.The imaging of last conventional M type is merely able to observe heart from a sample line direction, spatially analyzes not comprehensive.Because the sample line of anatomy M shape imaging is not the scanning line of a reality but user-defined, the advantage of the conventional M type of reservation imaging that therefore can part can be improved its deficiency again.
Philips company has just submitted the patent application (US 6,589,175 B2) that name is called " the in real time any M type (Real-Time Arbitrary M-Mode for Ultrasonic Imaging System) on the ultrasonic image-forming system " in 2003.This patent disclosure device block diagram as shown in Figure 1, this device comprises: two memory caches of preserving scan-line datas, and two image buffer storages of preserving the M line data after the conversion.The N bar scan-line data that front end and memory cache cooperation, front end form wave beam is as one group, alternative being kept in two memory caches, and this N bar scanning line is exactly the scanning line of sample line process; Scan conversion is responsible for M type data wire of N bar scanning line conversion generation of memory cache alternately is kept in the image buffer storage, and image buffer storage carries out M figure demonstration with showing cooperation.
The main thought of above-mentioned US 6,589,175 patents is to be divided into repeatedly and to scan by scanning a two field picture process, scans some lines at every turn, at twice the scanning line of interval scan M sample line process of being separated by, thereby improves the frequency that obtains M figure.The technical scheme of Philips will obtain the B diagram data and the anatomy M shape data wire is separated, and its shortcoming is: to sacrifice B figure frame per second is that cost reaches the effect that improves M figure frame per second.We carry out simple a calculating, just know the Philips scheme for the dissection M data that obtain specific frame per second the B figure frame per second that must sacrifice, suppose that the sample line span is a N bar scanning line, scan a line and need 0.25 millisecond, one frame B figure has 120 lines, the frame per second of M figure requires to reach F frame/second, can calculate then that B figure frame per second is when not carrying out anatomy M shape
B schemes original frame per second: 1000/ (0.25120)=33 frame/second,
Generate the time that M line data are spent: N*F*0.00025 in 1 second,
The remaining time that is used to generate B figure: (1-N*F*0.00025).
Be easy to calculate, if F was 60 frame/seconds, sample line span N is 20 lines, and then B frame per second remaining 23 frame/seconds, B image frame per second depends on the span of scanning line, and owing to B image frame per second makes that to the dependence of N the frame per second of system is unpredictable.
Because many external major companies generally use medium-to-high grade machine, frame per second is original just very high, therefore do not need when realizing anatomy M shape to consider that frame per second is low to dissecting the influence of M image, the present invention is intended to solve the problem that how realizes anatomy M shape imagings at the not high low and middle-grade machines of frame per second.
Summary of the invention
The technical problem to be solved in the present invention is to propose a kind of ultrasonic B imaging system based on low frame per second, under the prerequisite that does not reduce B figure frame per second, by the B diagram data being carried out the method and apparatus that interpolation obtains mimic high frame per second M type image.
The present invention adopts following technical scheme: design a kind of ultrasonic B imaging data processing method for acquisition anatomy M shape image, this method, is characterized in that comprising the steps: as hardware foundation with ultrasonic image-forming system
A. the tested body tissue of main controller controls alignment probe transmits and receives ultrasound wave in the mode every (K-1) column split scanning, described mode every (K-1) column split scanning is meant scanning line is divided into the K group, the i group is by i, K+i, 2K+i, 3K+i, ... the column scan line is formed, described probe transmits and receives the ultrasonic signal of each group one by one in order since first group, and the ultrasonic signal of i-1 group shifts to an earlier date δ t second in time than the ultrasonic signal of i group, i=1 wherein, K, therefore, a frame B diagram data is divided on time series continuous, but spatial resolution has reduced K K group data doubly;
B. described K group ultrasonic echo scanning-line signal enters beam synthesizer successively, is finished being admitted to the detector detection after focusing is delayed time, the weighted sum passage is sued for peace by beam synthesizer, and the output signal of detector is stored at least one data buffering;
C.B type scan conversion module (BDSC) is transferred the K group data in the described data buffering, allows K group data be combined together to form whole frame B data, and this frame B data are stored in the B image buffers and show the B figure by display;
D.M type scan conversion module (MDSC) is also transferred K group data from described data buffering, obtain a M type data wire from every group of data, forms the gridden data of K time scale anatomy M shape under the degree of depth-time coordinate system that continues to use family custom scan line;
E. improve temporal resolution by between two data wires of adjacent time, carrying out interpolation;
F. be stored into the M image buffers and show anatomy M shape figure through the anatomy M shape Data Update after the e step interpolation by described display;
Repeating step a obtains the anatomy M shape figure of empty sequence when whole to step f.
The span of described K is 2 to 10, in an embodiment of the present invention, K value 2, promptly pop one's head in to divide the mode of two groups of scannings to transmit and receive ultrasound wave every row, described interpolation method adopts linear interpolation or spline interpolation, need to insert the Newfps/Orgfps data lines between the M type data wire of described two adjacent intervals, temporal resolution through anatomy M shape data after the interpolation is Newfps, wherein Orgfps is the original frame per second of M type data, and Newfps is the target frame rate that the needs according to the anatomy M shape pictorial display set.As a rule, described Newfps/Orgfps is not an integer, and therefore the interpolation between the M type data wire of two adjacent intervals is the non-integral multiple interpolation of equal time distance.If Newfps/Orgfps is an integer, then the interpolation between the M type data wire of two adjacent times is that equal time is apart from the integral multiple interpolation.
The technical scheme that technical solution problem of the present invention is adopted also comprises: design a kind of device that utilizes the ultrasonic B imaging data to obtain the anatomy M shape image, comprising:
A front end assemblies, comprise beam synthesizer, with the unidirectional probe that is connected of this beam synthesizer input with the unidirectional detector that is connected of described beam synthesizer outfan, be used for launching ultrasound wave and receiving the ultrasound echo signal that tested body tissue reflects to tested body tissue, this ultrasound echo signal is finished by described beam synthesizer and is admitted to described detector detection after focusing is delayed time, the weighted sum passage is sued for peace;
A master controller is used to control front end assemblies and transmits and receives hyperacoustic mode and device is handled the ultrasound echo signal enforcement control that tested body tissue reflects;
At least one data buffering, the ultrasonic echo data that is used to store described detector output calls for signal processing module;
Flame Image Process and display module are used for the M type data of described data buffering are carried out Type B image and anatomy M shape treatment of picture and demonstration respectively, it is characterized in that:
Described master controller transmits and receives ultrasound wave by the control probe in the mode every (K-1) column split scanning, make the higher frame Type B data of spatial resolution be divided into successive data on time series, every group of data can be regarded the lower B diagram data of a spatial resolution as;
Described Flame Image Process and display module comprise two independently anatomy M shape graphics processing unit and Type B graphics processing units mutually; Described anatomy M shape graphics processing unit comprises interpolating module, M-scan conversion module (MDSC) that is connected with this interpolating module input and the M image buffers that is connected with described interpolating module outfan, be used for the M type data that access from data buffering are carried out Coordinate Conversion by the scan conversion module, the degree of depth-time coordinate that family custom scan line is continued to use in formation is the gridden data of the anatomy M shape of following K time scale, by described interpolating module the gridden data of this anatomy M shape is carried out the temporal resolution of interpolation with further raising anatomy M shape data then, the anatomy M shape Data Update after this interpolation is stored into described M image buffers and shows M type image by display; Described Type B graphics processing unit comprises B-scan conversion module (BDSC), the B image buffers that is connected with this B-scan conversion module (BDSC) outfan, be used for the K of data buffering group data are combined together to form the whole frame Type B data row-coordinate conversion of going forward side by side, the Type B data of this frame after conversion are updated and are stored in described B image buffers and show the Type B image by display.
As a specific embodiment, described master controller transmits and receives ultrasound wave by the control probe in the mode every column split scanning, and promptly the K value is 2, and described data buffering has two, data buffering a and data buffering b, two data bufferings are respectively deposited one group of data from detector output.
Compared with prior art, the method and apparatus that the present invention utilizes the ultrasonic B imaging data to obtain the anatomy M shape image has following advantage: carry out non-integral multiple linear interpolation by the gated sweep mode with to data, guaranteeing under the constant situation of Type B image frame per second, obtain higher anatomy M shape frame per second, make and realize that on low and middle-grade B ultrasonic machines anatomy M shape imaging becomes possibility.
Description of drawings
Fig. 1 is the existing theory diagram of realizing the ultrasonic B imaging system of anatomy M shape image;
Fig. 2 is the system block diagram of existing ultrasonic B imaging device;
Fig. 3 is that the present invention utilizes the ultrasonic B imaging data to obtain the theory diagram of the device of anatomy M shape image;
Fig. 4 is the sketch map of anatomy M shape image sampling line;
Fig. 5 is each sketch map every the column scan emission control;
Fig. 6 is the sketch map of MDSC module scanning emission control;
Fig. 7 is the sketch map of non-integer interpolation method;
Fig. 8 is the flow chart of non-integer interpolation method.
The specific embodiment
Below in conjunction with the most preferred embodiment shown in accompanying drawing and the accompanying drawing apparatus of the present invention and method are described in further detail.
Understand existing ultrasonic image-forming system earlier and will help understanding and recoganization apparatus of the present invention.Fig. 2 is the system block diagram of existing ultrasonic B imaging device, and probe afterwards, receives the ultrasound wave that reflects from tested body tissue again to tested body tissue emission ultrasound wave; Echo-signal enters beam synthesizer, is finished focusing on time-delay, the summation of weighted sum passage by beam synthesizer.The output signal of beam synthesizer is detected by detector, and detector is given the DSC scan converter with signal and finished coordinate transform, gives display at last and shows the single-frame images data, and all controls of ultrasonic imaging apparatus are all finished by master controller.
Fig. 3 is that the present invention utilizes the ultrasonic B imaging data to obtain an embodiment of the device of anatomy M shape image, and this device comprises:
A master controller is used to control front end assemblies and transmits and receives hyperacoustic mode and device is handled the ultrasound echo signal enforcement control that tested body tissue reflects;
A front end assemblies, comprise beam synthesizer, with the unidirectional probe that is connected of this beam synthesizer input with the unidirectional detector that is connected of described beam synthesizer outfan, be used for launching ultrasound wave and receiving the ultrasound echo signal that tested body tissue reflects to tested body tissue, this ultrasound echo signal is finished by described beam synthesizer and is admitted to described detector detection after focusing is delayed time, the weighted sum passage is sued for peace; Though it is identical that above-mentioned hardware is formed with the prior art of Fig. 2, but its working method has huge difference in essence, the master controller of present embodiment transmits and receives ultrasound wave by the control probe in the mode every column split scanning, promptly pass through the order of main controller controls front end emission received scanline, make the higher frame B diagram data of spatial resolution be divided into successive 2 groups of data on time series, the lower B view data of resolution when these two groups of data can be regarded as;
At least one data buffering, the ultrasonic echo data that is used to store described detector output calls for signal processing module; Present embodiment is provided with two data bufferings, and data buffering a and data buffering b respectively deposit one group of M type data from detector output.The data buffering that each group data separately leaves in has separately made things convenient for calling of data.If the form to data stipulated, cushion with data that to store whole data also passable.
Flame Image Process and display module are used for the data of described data buffering are carried out Type B image and anatomy M shape treatment of picture and demonstration respectively, and it comprises two independently anatomy M shape graphics processing unit and Type B graphics processing units mutually.Described anatomy M shape graphics processing unit comprises interpolating module, M-scan conversion module (MDSC) that is connected with this interpolating module input and the M image buffers that is connected with this interpolating module outfan, be used for alternatively obtaining data and carrying out Coordinate Conversion from data buffering a and data buffering b respectively by the scan conversion module, the gridden data of two time scales of anatomy M shape under the degree of depth of family custom scan line-time coordinate system is continued to use in formation, by described interpolating module the gridden data of this anatomy M shape is carried out the temporal resolution of non-integral multiple interpolation with further raising anatomy M shape data then, the anatomy M shape Data Update after this interpolation is stored into described M image buffers and shows M type image by display; Described Type B graphics processing unit comprises B-scan conversion module (BDSC), the B image buffers that is connected with this B-scan conversion module (BDSC) outfan, being used for two groups of M type data of data buffering a and data buffering b are combined obtains the whole frame Type B data row-coordinate conversion of going forward side by side, and this frame is updated through the Type B data of conversion and is stored in described B image buffers and shows the Type B image by display.
Though what it is pointed out that embodiments of the invention (Fig. 3) description is a system block diagram under the B|M pattern, be easy to apparatus of the present invention popularization is extended to the real-time anatomy M shape figure of realization under other pattern.
Be illustrated as the ultrasonic B imaging data processing method that obtains the anatomy M shape image with ultrasonic image-forming system shown in Figure 3 as hardware foundation, this method comprises the steps:
The tested body tissue of step a. main controller controls alignment probe transmits and receives ultrasound wave in the mode every (K-1) column split scanning, described mode every (K-1) column split scanning is meant scanning line is divided into the K group, the i group is by i, K+i, 2K+i, 3K+i, ... the column scan line is formed, and described probe transmits and receives the ultrasonic signal of each group one by one in order since first group, the ultrasonic signal of i-1 group shifts to an earlier date δ t second in time than the ultrasonic signal of i group, i=1 wherein, K, therefore, the higher frame B diagram data of spatial resolution is divided into successive K group data on time series, and the span of K is 2 to 10.Though K is big more in theory, the M frame per second can be high more, considers the balance of frame per second and picture quality, according to practical application suitable K value determined in the requirement of image.For present embodiment, the value of K is 2, promptly is the embodiment every the column scan emission control, as shown in Figure 5.L1～L8 is a scanning line among the figure, shooting sequence is preface scanning successively from L1 to L8 under the regular situation, the inventive method adopts every the column scan method, scan singular line scanning line L1-earlier〉L3-〉L5-〉L7, scan amphitene scanning line L2-then〉L4-〉L6-〉L8, system is stored in data buffering a and data buffering b respectively with scan-line data, and data buffering a has just preserved the singular line data like this, and data buffering b has preserved the amphitene data.Example among the figure is that a frame figure is made of eight scan-line datas, and scan-line data can be much more in the reality, but certain simplification has been carried out in not variation of scan method here.It is in order to obtain many M image sampling line data from a frame B image that shooting sequence is changed, because the B image is to the requirement of the spatial resolution requirement greater than temporal resolution, and the anatomy M shape image is opposite, and its requirement to temporal resolution is higher; By every column scan, that the odd and even data line is expressed respectively is the B figure that a frame scan line reduces by half, its spatial resolution has reduced, but we can obtain two sample line data continuous in time from these two groups of data, and for B figure, the parity line group combines, remaining number of scanning lines does not have the B that changes to scheme, and the scan period does not change, therefore the B frame per second does not change yet, by this method, we obtain the data more than the anatomy M shape data wire of a frame in the time cycle of scanning one frame B figure.
The described two groups of ultrasound echo signals of step b. enter beam synthesizer, are finished being admitted to the detector detection after focusing is delayed time, the weighted sum passage is sued for peace by beam synthesizer, and two groups of output signals of detector are kept at respectively among data buffering a and the data buffering b;
Step c B-scan conversion module (BDSC) is transferred two groups of data among described data buffering a and the data buffering b respectively, allows two groups of data be combined together to form whole frame B data, and this frame B data are stored in the B image buffers and show the B figure by display; As shown in Figure 4, the left side is to carry out the preceding B figure in data buffering of Coordinate Conversion (BDSC), the right is to carry out the B figure that Coordinate Conversion (BDSC) back forms, line segment L is to be the sample line of end points with P1P2 shown in Fig. 4 the right, the definition of this sample line can be defined by the user by pulley mouse or alternate manner, in addition, though the line segment that shows among this figure is a straight line, but the present invention does not limit to and straightway, also can be curve sample line situation.Also shown the corresponding lines L ' in the data buffering of L before the BDSC conversion among the figure, the corresponding P1 ' of P1, the corresponding P2 ' of P2.
Steps d .M type scan conversion module (MDSC) is also transferred the go forward side by side row-coordinate conversion of two groups of data from described data buffering, form the gridden data of two time scale anatomy M shapes under one time of the degree of depth coordinate system of continuing to use family custom scan line; Fig. 6 is the effect signal of MDSC module, the left side be scan-line data among the data buffering a (b), scanning line uses solid line to represent, lines L ' is user-defined sample line simultaneously, the MDSC module is sampled on L ' uniformly and is arranged, from data buffering a (b), obtain a sample line data I, the needs decision that sampling number shows according to actual M figure.
Step e. improves temporal resolution by carry out interpolation between two data wires of adjacent time; Introduce below and how to carry out interpolation.
The hypothetical target frame per second is the frame per second that the demonstration of anatomy M shape needs, and original frame per second is the frame per second that obtains the M data wire, in conventional M type, owing to be a scan-line data, therefore common original frame per second can be much higher than target frame rate, by the relevant image that can obtain target frame rate of frame.But for anatomy M shape, because the multi-strip scanning line could obtain line data, if therefore target frame rate just needs the interpolating module interpolation to obtain the frame per second of needs greater than original frame per second.If target frame rate is the integral multiple of original frame per second, be exactly the integral multiple interpolation so, for the integral multiple interpolation, the actual line data that obtain are video data lines in the M image as a result, thus every acquisition two line data just between insert some data wire formation figure as a result.
In practice, original frame per second and target frame rate all are fixed, and generally are not the integral multiple relations, therefore obtain the target frame rate image by non-integral multiple interpolation method.If original frame per second was 25 frame/seconds, target frame rate was 128 frame/seconds, multiple has been exactly 5.12 times so, suppose to show that dissecting M figure size is 512 data wires, so every data wire all corresponding a time scale, and the line data of original acquisition are not corresponding this scale basically, and therefore for non-integral multiple interpolation, the real data line generally is not the data wire of actual displayed.Fig. 7 is the sketch map of non-integral multiple interpolation.Solid line I1～I3 among the figure is by the actual data wire that obtains in MDSC conversion back, and the needs interpolation data presented line of dotted line M1～M5 for calculating according to target frame rate and original frame per second, the line number that inserts between two solid lines is possible different.
We are the position that benchmark calculates interpolation number of lines and interpolation line with the time scale.Suppose that Orgfps is original frame per second, Newfps is a target frame rate, need to insert the Newfps/Orgfps data lines between the M type data wire of described two adjacent intervals, if the temporal resolution of the M type data before the interpolation is δ t, then the temporal resolution through anatomy M shape data after the interpolation is Newfps, every adjacent two actual data wires that obtain are calculated the coordinate line scale iLf and the iRt of its directions X (representative time) in the dissection M figure that will show, [iLf so, iRt] between integer be exactly the data wire that will insert between these two real data lines, use interpolation scheme to carry out interpolation to belonging to this interval data wire then.ILf and iRt can try to achieve by following formula:
iLf＝(i-1)*Newfps/Orgfps
iRt＝i*Newfps/Orgfps
Just can carry out interpolation after having known the relation of the data wire that needs interpolation and the actual data wire that obtains, interpolation method can use various interpolation algorithms as required, such as linear interpolation, and spline interpolation, perhaps self-defining interpolation algorithm or the like.What the embodiment of the invention was used is linear interpolation, because linear interpolation algorithm is simple, realizes by hardware easily, can carry out interpolation arithmetic fast.
Non-integral multiple plug wire process as shown in Figure 8.In the zero hour, assignment I=0, iLf=1, read the data of single line, carry out following circulation then: the circulation beginning: compose I=I+1, obtain the time scale iRt at I velamen interpolation line place then, to [iLf, iRt] between the integer line carry out interpolation, make iLf=iRt after interpolation is finished, get back to the circulation starting position again and carry out new round interpolation process.
Anatomy M shape Data Update after the step f. process e step interpolation is stored into the M image buffers and shows anatomy M shape figure by described display;
Repeating step a obtains the anatomy M shape figure of empty sequence when whole to step f.
Claims (8)
1, a kind of for obtaining the ultrasonic B imaging data processing method of anatomy M shape image, this method, is characterized in that comprising the steps: as hardware foundation with ultrasonic image-forming system
A. the tested body tissue of main controller controls alignment probe transmits and receives ultrasound wave in the mode of (K-1) column split scanning at interval, the mode of described interval (K-1) column split scanning is meant scanning line is divided into the K group, the i group is by i, K+i, 2K+i, 3K+i, ... the column scan line is formed, and described probe transmits and receives the ultrasonic signal of each group one by one in order since first group, the ultrasonic signal of i-1 group shifts to an earlier date δ t second in time than the ultrasonic signal of i group, i=1 wherein ..., K, therefore, a frame B diagram data is divided on time series continuous, but spatial resolution has reduced K K group data doubly;
B.K group ultrasonic echo scanning-line signal enters beam synthesizer, is finished being admitted to the detector detection after focusing is delayed time, the weighted sum passage is sued for peace by beam synthesizer, and the output signal of detector is stored at least one data buffering;
C.B type scan conversion module is transferred the K group data in the described data buffering, allows K group data be combined together to form whole frame B data, and this frame B data are stored in the B image buffers and by display and show;
D.M type scan conversion module is also transferred K group data and obtain a M type data wire from every group of data from described data buffering, form the gridden data of K time scale anatomy M shape under the degree of depth-time coordinate system that continues to use family custom scan line;
E. improve temporal resolution by carrying out interpolation between two data wires to the adjacent time in the steps d;
F. be stored in the M image buffers and through the anatomy M shape data in real time updating value after the step e interpolation and show anatomy M shape figure by described display real-time update;
Repeating step a obtains the anatomy M shape figure of empty sequence when whole to step f.
2, according to claim 1 it is characterized in that: the span of K is 2 to 10 in order to obtain the ultrasonic B imaging data processing method of anatomy M shape image, and described interpolation adopts linear interpolation or spline interpolation.
3, according to claim 1 and 2 for obtaining the ultrasonic B imaging data processing method of anatomy M shape image, it is characterized in that: in step e, need to insert the Newfps/Orgfps data lines between two data wires of described adjacent time, temporal resolution through anatomy M shape data after the interpolation is Newfps, wherein Orgfps is the original frame per second of M type data, and Newfps is the target frame rate that sets according to anatomy M shape pictorial display needs.
4, according to claim 3 for obtaining the ultrasonic B imaging data processing method of anatomy M shape image, it is characterized in that: described Newfps/Orgfps is not an integer, and the interpolation between two data wires of described adjacent time is the non-integral multiple interpolation of equal time distance.
5, according to claim 3 it is characterized in that: described Newfps/Orgfps is an integer in order to obtain the ultrasonic B imaging data processing method of anatomy M shape image, and the interpolation between two data wires of described adjacent time is that equal time is apart from the integral multiple interpolation.
6, according to claim 2 it is characterized in that: described data buffering has two in order to obtain the ultrasonic B imaging data processing method of anatomy M shape image, and data buffering a and data buffering b are used for storing first group of M type data and second group of M type data respectively.
7, a kind of device that utilizes the ultrasonic B imaging data to obtain the anatomy M shape image, comprise: a front end assemblies, comprise beam synthesizer, with the unidirectional probe that is connected of this beam synthesizer input with the unidirectional detector that is connected of described beam synthesizer outfan, be used for launching ultrasound wave and receiving the ultrasound echo signal that tested body tissue reflects to tested body tissue, this ultrasound echo signal is finished by described beam synthesizer and is admitted to described detector detection after focusing is delayed time, the weighted sum passage is sued for peace;
A master controller is used to control front end assemblies and transmits and receives hyperacoustic mode and device is handled the ultrasound echo signal enforcement control that tested body tissue reflects;
At least one data buffering, the ultrasonic echo data that is used to store described detector output calls for signal processing module;
Flame Image Process and display module are used for the M type data of described data buffering are carried out Type B image and anatomy M shape treatment of picture and demonstration respectively, it is characterized in that:
Described master controller transmits and receives ultrasound wave by the control probe in the mode that interval (K-1) column split scans, and makes the higher frame Type B data of spatial resolution be divided into successive K group data on time series;
Described Flame Image Process and display module comprise two independently anatomy M shape graphics processing unit and Type B graphics processing units mutually; Described anatomy M shape graphics processing unit comprises interpolating module, M-scan conversion module that is connected with this interpolating module input and the M image buffers that is connected with described interpolating module outfan, be used for the M type data that access from data buffering are carried out Coordinate Conversion by the scan conversion module, the degree of depth-time coordinate that family custom scan line is continued to use in formation is the gridden data of the anatomy M shape of following K time scale, by described interpolating module the gridden data of this anatomy M shape is carried out the temporal resolution of interpolation with further raising anatomy M shape data then, the anatomy M shape Data Update after this interpolation is stored into described M image buffers and shows M type image by display; Described Type B graphics processing unit comprises B-scan conversion module, the B image buffers that is connected with this B-scan conversion module outfan, be used for the K of data buffering group data are combined together to form the whole frame Type B data row-coordinate conversion of going forward side by side, the Type B data of this frame after conversion are updated and are stored in described B image buffers and show the Type B image by display.
8, the device that utilizes the ultrasonic B imaging data to obtain the anatomy M shape image according to claim 7, it is characterized in that: described master controller transmits and receives ultrasound wave by the control probe in the mode every column split scanning, be that the K value is 2, described data buffering has two, be data buffering a and data buffering b, two data bufferings are respectively deposited one group of data from detector output.
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| CN101810492B (en) * | 2009-02-24 | 2013-10-02 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic diagnosis system, method for dynamically increasing imaging frame rate and beam synthesizer |
| CN103654868B (en) * | 2012-09-20 | 2016-08-31 | 飞依诺科技(苏州)有限公司 | The formation method of ultrasonic diagnostic equipment and system |
| CN103519845B (en) * | 2013-10-12 | 2015-03-04 | 清华大学 | Method and system for time alignment of acquisition and scanning regions of high frame frequency data of images |
| CN108113702A (en) * | 2017-12-21 | 2018-06-05 | 飞依诺科技(苏州)有限公司 | A kind of ultrasonic scanning method and apparatus |
| CN109044398B (en) * | 2018-06-07 | 2021-10-19 | 深圳华声医疗技术股份有限公司 | Ultrasound system imaging method, device and computer readable storage medium |
| CN112971857B (en) * | 2021-04-27 | 2021-08-27 | 深圳华声医疗技术股份有限公司 | Ultrasonic anatomical M imaging method, device and medium |
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Application publication date: 20070307 Assignee: Shenzhen Mindray Animal Medical Technology Co.,Ltd. Assignor: SHENZHEN MINDRAY BIO-MEDICAL ELECTRONICS Co.,Ltd. Contract record no.: X2022440020009 Denomination of invention: Method and apparatus for obtaining anatomical M-mode images using ultrasound B-mode imaging data Granted publication date: 20090408 License type: Common License Record date: 20220804 |