CN102283679B - Ultrasonic imaging system for elasticity measurement and method for measuring elasticity of biological tissue - Google Patents
Ultrasonic imaging system for elasticity measurement and method for measuring elasticity of biological tissue Download PDFInfo
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- CN102283679B CN102283679B CN201110222813.1A CN201110222813A CN102283679B CN 102283679 B CN102283679 B CN 102283679B CN 201110222813 A CN201110222813 A CN 201110222813A CN 102283679 B CN102283679 B CN 102283679B
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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
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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
- A61B8/0833—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures
- A61B8/085—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures for locating body or organic structures, e.g. tumours, calculi, blood vessels, nodules
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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
- A61B8/0825—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of the breast, e.g. mammography
Abstract
The invention relates to an ultrasonic imaging system for elasticity measurement. The ultrasonic imaging system comprises a probe, an ultrasonic imaging device, a controlling and processing device and a display device, wherein the probe comprises a low-frequency oscillation driving device for generating oscillation and forming a shearing wave propagating from human body surface to tissues, and an ultrasonic transducer array for sending an ultrasonic signal to the tissues and receiving an ultrasonic echo signal; the ultrasonic imaging device is used for driving the ultrasonic transducer array to send the ultrasonic signal and receive and process the ultrasonic echo signal according to loaded imaging parameters; the controlling and processing device is used for controlling the low-frequency oscillation driving device and the ultrasonic imaging device to process the ultrasonic echo signal so as to obtain a two-dimensional ultrasonic image and elasticity information of the tissues; and the display device is used for displaying the two-dimensional ultrasonic image and the elasticity information. The system and elasticity measuring method can simultaneously obtain the two-dimensional ultrasonic image and the elasticity information of the tissues, thereby improving clinical diagnosis accuracy; and the probe can realize precise positioning under the guiding of the two-dimensional ultrasonic image without considering displacement compensation, thereby improving convenience and accuracy of tissue elasticity measurement.
Description
[technical field]
The present invention relates to ultrasonic imaging technique, particularly relate to a kind of method of ultrasonic image-forming system and measurement biological tissue elasticity of elasticity measurement.
[background technology]
The ultra sonic imaging of traditional B type is take the physiological structure information of obtaining biological tissue as main, insensitive to early lesion, but in early days when pathological changes the mechanical characteristics of biological tissue there is obvious variation.The mechanical characteristics such as the elastic modelling quantity (hardness) of biological tissue depend on molecular composition and the corresponding microstructure of biological tissue, and be closely related with its physiopathology characteristic; pathological tissues and normal structure often exist the difference of the mechanical characteristics such as elastic modelling quantity (hardness), therefore the mechanical characteristics of detection of biological tissue changes can provide important evidence for the diagnosis of numerous disease.
Ultrasonic Elasticity Imaging is the Novel ultrasonic diagnosing image technology of rising in recent years, utilizes ultrasonic signal to follow the tracks of the deformation data of the stressed front and back of biological tissue, and then obtains the mechanical characteristics such as strain, modulus of shearing and the elastic modelling quantity of biological tissue.Due to biological tissue's pathological changes and its mechanical characteristics closely related, therefore ultrasonic elastograph imaging can provide important auxiliary information for the diagnosis of ultra sonic imaging, for example, ultrasonic elastograph imaging has boundless application prospect at aspects such as staging diagnosis, atheromatous plaque early diagnosis, radiofrequency ablation therapy and the monitoring of breast cancer detection, hepatic fibrosis and liver cirrhosis.
Ultrasonic Elasticity Imaging is developed so far and derives how many kinds of method, can be divided into static elastogram, dynamic elastic imaging, transient state elastogram and long-range elastogram according to the difference of force mechanism.Ultrasonic Elasticity Imaging is according to mechanical wave conduction velocity and organize hardness, the principle that elastic modelling quantity is relevant, adopt the method for transient state elastogram that hepatic fibrosis and liver cirrhosis are detected and quantized, its method is as follows: a single array element ultrasonic transducer is integrated on the vibrating shaft of an audio oscillator, formation shearing wave probe, the instantaneous low frequency and amplitude vibration that audio oscillator sends forms shearing wave in biological tissue, cause that micro-displacement and deformation occur in biological tissue, the deformation of recording biological tissue launched ultrasound wave and receives echo-signal by ultrasonic transducer simultaneously, to extract the displacement information of biological tissue, further obtain the propagation condition of shearing wave in biological tissue, because shearing wave propagation condition and biological tissue elasticity modulus are contacted directly, thereby can calculate and obtain modulus of shearing and elastic modelling quantity by shearing wave spread speed.The elastic modelling quantity of hepatic tissue increases along with the development of hepatic fibrosis and liver cirrhosis has significantly, and therefore this method has good sensitivity and specificity.Ultrasonic Transient elastography is a kind of noinvasive, fast and have hepatic fibrosis and a liver cirrhosis quantitative detecting method of better repeatability.But Ultrasonic Elasticity Imaging is that device or method are all comparatively complicated, the difficulty of realization is also larger, unusual inconvenience in the process of obtaining biological tissue elasticity information.
[summary of the invention]
Based on this, be necessary to provide a kind of ultrasonic image-forming system of the elasticity measurement that improves convenience.
In addition, be also necessary to provide a kind of method of the measurement biological tissue elasticity that improves convenience.
A ultrasonic image-forming system for elasticity measurement, comprises probe, supersonic imaging device, control and blood processor and display device;
Described probe comprises:
Low-frequency oscillation driving device, for generation of the shearing wave that vibrates and form the propagation from body surface to organization internal;
Ultrasound transducer array, for launching ultrasonic signal to tissue, and tissue receiving ultrasound echo signal;
Supersonic imaging device, for according to loaded imaging parameters, drives described ultrasound transducer array to launch ultrasonic signal to biological tissue, and receives and process the ultrasound echo signal from described ultrasound transducer array; ;
Control and blood processor, for controlling described low-frequency oscillation driving device and supersonic imaging device, process the two-dimensional ultrasonic image and the elastic information that obtain described tissue from the ultrasound echo signal of described supersonic imaging device;
Display device, for showing two-dimensional ultrasonic image and the elastic information of described tissue.
Preferably, described ultrasound transducer array comprises multiple ultrasonic transducer array element, and the centre position of described ultrasound transducer array offers through hole, and the vibrating shaft of described low-frequency oscillation driving device is through described through hole.
Preferably, described through hole and described vibrating shaft match.
Preferably, the length that described vibrating shaft stretches out through described through hole is 0.5～1.5 millimeter.
Preferably, described low-frequency oscillation driving device is audio oscillator or motor.
Preferably, described ultrasound transducer array is any one in linear array ultrasonic transducer, protruding battle array ultrasonic transducer or phase array transducer.
Preferably, described supersonic imaging device comprises ultrasound emission module, ultrasonic receiver module and transmitting receiving key circuit;
Described ultrasound emission module is used for driving described ultrasound transducer array transmitting ultrasonic signal;
Described ultrasonic receiver module receives echo-signal for receiving and process described ultrasound transducer array;
Described transmitting receiving key circuit is for isolated high-voltage.
Preferably, described control and blood processor, also for the control of the Oscillation Amplitude to described low-frequency oscillation driving device, frequency, time, provide the parameter control of ultra sonic imaging, and process the ultrasound echo signal from described supersonic imaging device.
Preferably, described supersonic imaging device loads the imaging parameters that described control and blood processor provide, and for driving described ultrasound transducer array transmitting ultrasonic signal, receives and process described ultrasound transducer array ultrasound echo signal and carry out wave beam synthetic.
Preferably, the ultrasound echo signal of described supersonic imaging device after wave beam is synthetic enters described control and blood processor, obtains the Real-time Two-dimensional ultrasonoscopy of tissue through the processing of described control and blood processor.
A method of measuring biological tissue elasticity, comprises the steps:
Utilize the Real-time Two-dimensional ultrasonoscopy of biological tissue to position, determine biological tissue region to be detected;
Control the generation of low-frequency oscillation driving device and vibrate and form the shearing wave from body surface to described biological tissue internal communication, induce described biological tissue that miniature deformation occurs;
Utilize the each a part of ultrasonic transducer array element in vibrating shaft left and right, according to controlling and the parameter that provides of blood processor postpones and the high pulse repetition frequency of 1kHz～10KHz is launched ultrasonic signal and receives ultrasound echo signal, described ultrasound echo signal synthesizes the ultrasonic signal sequence of formation along vibrating shaft center position by wave beam;
Utilize elastogram algorithm process and calculate described ultrasonic signal sequence the elastic information that obtains biological tissue region to be detected;
Show the elastic information in described biological tissue region to be detected.
Preferably, the described step of utilizing elastogram algorithm process and the described ultrasonic signal sequence of calculating to obtain the elastic information in biological tissue region to be detected comprises:
Described ultrasonic signal sequence is carried out to filtering;
Calculate and propagate by shearing wave the displacement of tissue causing according to described filtered ultrasonic signal sequence;
Described displacement of tissue is carried out to smothing filtering and matched filtering;
According to the strain of described displacement of tissue computation organization;
Organize strain to calculate shearing wave spread speed in described biological tissue by described;
Calculate the elastic modelling quantity of described biological tissue according to shearing wave spread speed and empirical equation in described biological tissue.
The method of the ultrasonic image-forming system of above-mentioned elasticity measurement and measurement biological tissue elasticity can obtain two-dimensional ultrasonic image and the tissue elasticity information organized simultaneously, improves clinical diagnosis accuracy; Probe can be realized accurately location under two-dimensional ultrasonic image guiding, low-frequency oscillation driving device and ultrasound transducer array are relatively independent, ultrasound transducer array can't move along with low-frequency oscillation driving device, even if ultrasound transducer array is because small movements has occurred low-frequency oscillation driving device, computing in the time carrying out strain estimation also can be offset the displacement that ultrasound transducer array small movements causes, therefore need not consider bit shift compensation, improve convenience and accuracy that tissue elasticity is measured, reduced the difficulty of processing.
[accompanying drawing explanation]
Fig. 1 is the structural representation of the ultrasonic image-forming system of an embodiment Elastic measurement;
Fig. 2 is the structural representation of popping one's head in Fig. 1;
Fig. 3 is the structural representation at another visual angle of popping one's head in Fig. 2;
Fig. 4 launches the schematic diagram calculating with receive delay in an embodiment;
Fig. 5 is the method flow diagram of measuring biological tissue elasticity in an embodiment;
Fig. 6 utilizes elastogram algorithm calculating ultrasonic signal sequence to obtain the method flow diagram of the elastic information in biological tissue region to be detected in Fig. 5;
Fig. 7 is the two-dimensional ultrasonic image of liver in the actual use procedure of ultrasonic image-forming system of measuring of embodiment Elastic;
Fig. 8 is that the strain of white lines correspondence position in Fig. 7 is with the modified-image of the degree of depth and time.
[specific embodiment]
Fig. 1 shows the ultrasonic image-forming system that an embodiment Elastic is measured, and this system comprises probe 10, supersonic imaging device 310, control and blood processor 330 and display device 350.
Low-frequency oscillation driving device 110, for generation of the shearing wave that vibrates and form the propagation from body surface to organization internal.
In the present embodiment, low-frequency oscillation driving device 110 is audio oscillator or motor.For make biological tissue that miniature deformation occurs by external force or endogenetic process, there is low frequency and amplitude vibration by the vibrating shaft 111 in low-frequency oscillation driver 110, cause to the shearing wave of propagating in biological tissue and induce it that miniature deformation occurs.
If it is too high to shear wave frequency in low-frequency oscillation driving device 110, shearing wave decay is too low, if frequency is too low, diffraction effect is too strong, and everything is all unfavorable for shearing wave propagation.If shearing wave amplitude is too little in low-frequency oscillation driving device 110, make to propagate the degree of depth limited, shearing wave amplitude is too large, also can make human body have sense of discomfort, therefore in a preferred embodiment, the frequency of vibration that low-frequency oscillation driving device 110 produces is 10 hertz to 1000 hertz, and amplitude is 0.2 millimeter to 2 millimeters.
In the present embodiment, ultrasound transducer array 130 is any one in linear array ultrasonic transducer, protruding battle array ultrasonic transducer or phase array transducer.Ultrasound transducer array 130 contacts with human or animal's body surface, to get the two-dimensional ultrasonic image of biological tissue.The two-dimensional ultrasonic image obtaining in real time by ultrasound transducer array 130 is accurately located, auxiliary and guiding probe 10 is located accurately according to actual needs, particularly, the corresponding position of scanning line in two-dimensional ultrasonic image centre position is region to be detected, for the clinical Transient elastography process of reality provides accurate location.
Particularly, as shown in Figures 2 and 3, through hole is offered in the centre position of ultrasound transducer array 130, and the vibrating shaft 111 of low-frequency oscillation driving device 110 is through through hole.In the present embodiment, ultrasound transducer array 130 has comprised multiple transducer arrays without 133, and this ultrasound transducer array 130 center offers through hole (not shown), and the diameter of this through hole and vibrating shaft 111 match.The length that vibrating shaft 111 stretches out through through hole can not be oversize, if vibrating shaft 111 stretches out the oversize body surface that will make ultrasound transducer array 130 be difficult to touch human body or organism of the length of through hole, cannot imaging, the length that therefore vibrating shaft 111 stretches out through through hole is preferably 0.5～1.5 millimeter.
In the present embodiment, what supersonic imaging device 310 provided for Loading Control and blood processor 330 transmits and receives the imaging parameters such as delay, drives ultrasound transducer array 130 to launch ultrasonic signal, receives and process ultrasound echo signal and carry out wave beam synthetic.
The ultrasound echo signal of supersonic imaging device 310 after wave beam is synthetic enters to be controlled and blood processor 330, obtains the Real-time Two-dimensional ultrasonoscopy of tissue through the processing of this control and blood processor 330.
Particularly, supersonic imaging device 310 has comprised ultrasound emission module 311, ultrasonic receiver module 313 and transmitting receiving key circuit 315.Wherein, ultrasound emission module 311 is launched ultrasonic signal for controlling ultrasound transducer array 130, and ultrasonic receiver module 313 receives ultrasound echo signal for controlling ultrasound transducer array 130, and transmitting receiving key circuit 315 is for isolated high-voltage.
Control and blood processor 330, for controlling low-frequency oscillation driving device 110 and supersonic imaging device 310, process the two-dimensional ultrasonic image and the elastic information that obtain tissue from the ultrasound echo signal of supersonic imaging device 310.
In the present embodiment, control and blood processor 330, also for the control of the Oscillation Amplitude to low-frequency oscillation driving device, frequency, time, provide the parameter control of ultra sonic imaging, and process the ultrasound echo signal from supersonic imaging device 310.Particularly, control and blood processor 330 will calculate according to parameters such as ultrasonic propagation velocity, array element distance and investigation depths, to control the aspect such as opening time, shut-in time, pulse width and pulse recurrence rate of ultrasound transducer array 130.Control and blood processor 330 provides accurate parameter to carry out scanning type focus for supersonic imaging device 310.
In a preferred embodiment, control and blood processor 330 can be at least one in computer, single-chip microcomputer, field programmable gate array (Field-Programmable Gate Array is called for short FPGA) and arm processor.
Particularly, control and blood processor 330 comprise low-frequency oscillation driving control unit 331, ultra sonic imaging control unit 333 and signal processing unit 335.Low-frequency oscillation driving control unit 331 is for controlling low-frequency oscillation driving device 110; Ultra sonic imaging control unit 333 is used to supersonic imaging device 310 that imaging parameters is provided; Signal processing unit 335 is for the ultrasound echo signal receiving is carried out to imaging processing, and calculating elastic information.
As shown in Figure 4, control and blood processor 330 are according to the adjacent transducer array element distance d in ultrasound transducer array 130
e, the label transducer array element correspondence position that is n ultrasonic scanning line focus depth D
f, launch or receive the transducer array element at edge to the distance B of focus point at every turn
0, the label transducer array element that is i is to distance and the spread speed C of ultrasound wave in biological tissue of focus point, to being designated the ultrasonic scanning line of ultrasonic transducer array element correspondence position of i, transmitting postpones E
delaywith receive delay R
delaycalculate by following formula:
That is:
By controlling and the processing of blood processor 330 to transmitting delay and receive delay, ultrasonic signal is matched with the corresponding degree of depth.
Before ultrasonic elastograph imaging system is carried out elastogram, ultrasound transducer array 130 is also launched ultrasonic signal for the body surface to be measured to contact, and receives ultrasound echo signal; Control and blood processor 330 are also for forming the Real-time Two-dimensional ultrasonoscopy of body surface to be measured according to the ultrasound echo signal receiving; Probe 10, for positioning according to Real-time Two-dimensional ultrasonoscopy, is determined the region to be detected of body surface to be measured.
In the present embodiment, in the time carrying out ultrasonic elastograph imaging, first transmitting ultrasonic signal after the body surface that makes ultrasound transducer array 130 and human or animal body etc. contacts, and form the Real-time Two-dimensional ultrasonoscopy of body surface to be measured by the received ultrasound echo signal of ultrasound transducer array 130, and show by display device 350, now position at body surface to be measured according to the Real-time Two-dimensional ultrasonoscopy guiding probe 10 of body surface to be measured, to determine the region to be detected in body surface to be measured.
Fig. 5 shows the method for measuring biological tissue elasticity in an embodiment, comprises the steps:
Step S110, utilizes the Real-time Two-dimensional ultrasonoscopy of biological tissue to position, and determines biological tissue region to be detected.
Step S130, controls the generation of low-frequency oscillation driving device and vibrates and form the shearing wave from body surface to biological tissue's internal communication, and miniature deformation occurs in induction biological tissue.
Step S150, utilize the each a part of ultrasonic transducer array element in vibrating shaft left and right, according to controlling and the high pulse repetition frequency transmitting ultrasonic signal of the delay parameter that provides of blood processor and 1kHz～10KHz receive ultrasound echo signal, ultrasound echo signal synthesizes the ultrasonic signal sequence of formation along vibrating shaft center position by wave beam.
In the present embodiment, the pulse recurrence rate using is a higher pulse recurrence rate.
Step S170, utilizes elastogram algorithm process and calculates ultrasonic signal sequence the elastic information that obtains biological tissue region to be detected.
At one particularly in embodiment, as shown in Figure 6, above-mentioned utilize elastogram algorithm process and calculate the detailed process that ultrasonic signal sequence obtains the elastic information in biological tissue region to be detected be:
Step S171, carries out filtering to ultrasonic signal sequence.
In the present embodiment, low frequency and the radio-frequency component of the filtering that ultrasonic signal sequence is carried out in can filtering ultrasound echo signal.
Step S172, calculates and propagates by shearing wave the displacement of tissue causing according to filtered ultrasonic signal sequence.
In the present embodiment, adopt time domain cross-correlation, self correlation or other frequency processing method to carry out displacement of tissue estimation according to ultrasonic signal sequence, obtain propagating by shearing wave the displacement of tissue causing.
Step S173, carries out smothing filtering and matched filtering to displacement of tissue.
In the present embodiment, the singular point displacement composition suitable with shearing wave frequency with enhancing after the displacement of tissue that obtains estimation in filtering displacement of tissue.
Step S174, according to the strain of displacement of tissue computation organization.
In the present embodiment, the strain of biological tissue is calculated can adopt the methods such as method of least square, low-pass filtering calculus of finite differences or wavelet analysis, its objective is from the Displacements Distribution of biological tissue and obtain stress distribution, and reduce as far as possible the noise jamming of bringing due in difference (differential) process.
Step S175, by organizing strain to calculate shearing wave spread speed in biological tissue.
Step S176, calculates the elastic modelling quantity of biological tissue according to shearing wave spread speed and empirical equation in biological tissue.
Step S190, the elastic information in demonstration biological tissue region to be detected.
Below in conjunction with a specific embodiment elaborate and control and blood processor 330 carries out computing and obtain the process of tissue elasticity information to ultrasound echo signal sequence.In this embodiment, the ultrasonic signal of transmitting is 50 hertz, cycle T=300 μ s, and ultrasonic propagation velocity V=1500m/s, sample frequency f=60MHz, in one-period, ultrasound transducer array 130 samplings obtain T*F=18000 point.Because there is incident and reflection in fact hyperacoustic path, thereby be T*V/2=22.5cm in an incident degree of depth back and forth of echo.Experiment shows, in the subsequent treatment of echo-signal, and the 1000th～5000th of 18000 points that collect in each cycle, useful and enough.Sampling time overall length is t=0.1s, is equivalent to t/T=333 the cycle in ultrasonic signal, and therefore, the ultrasonic signal of getting 300 cycles wherein carries out analyzing and processing, to 4000 × 300 matrix analysis processing.
Before signal processing unit 335 starts cross correlation algorithm, first try to achieve two piece of data of doing Cross Correlation Matching, first part is above-mentioned 4000 × 300 array, the second piece of data is given up the first row data of original array, get its 2nd column data, 4000 totally o'clock the 1st row as the second piece of data, get the 3rd row of the first piece of data as the 2nd row of the second piece of data, and be listed as the 300th row as the second piece of data until get the 301st of the first piece of data by that analogy, finally obtain 4000 × 300 array.
For improving the degree of accuracy of Cross Correlation Matching, need first two piece of data that will carry out Cross Correlation Matching to be carried out respectively to bandpass filtering, then start Cross Correlation Matching algorithm.The window length of the cross correlation algorithm adopting is 100 points, and between window, Duplication is 90%, and step-length is 10 points.In actual algorithm, start matching operation using the first row of the first piece of data as the sliding shoe of the first row of matching template and the second piece of data.Template is made up of 200 points, 100 points that sliding shoe is template starting point institute correspondence position are as initial sliding piece, template starts matching operation with sliding shoe in same initial point position, after a matching operation finishes, sliding shoe is toward 1 point of depth direction slip, mate with template again, constantly repeat this process successively until the end point of sliding shoe moves to the end point of template, obtain the maximum of this matching result and the position at place thereof, after the relative displacement of this point of interpolation fitting, deposit result in relative displacement matrix.Then the initial position of template and sliding shoe is all moved to 10 points toward depth direction, again carry out above-mentioned matching process until the end at this columns strong point.So far, using the first row of the first piece of data as matching template with finish as the matching operation of sliding shoe using the first row of the second piece of data.Then start to carry out next one circulation, using the secondary series of the first piece of data as matching template with start the matching operation of a new round as sliding shoe using the secondary series of the second piece of data, circulate in this way until the Cross Correlation Matching computing between two piece of data finishes completely, obtain a relative displacement matrix, matrix size is 380 × 300.
For improving the degree of accuracy of Displacement Estimation, need to carry out the disposal of gentle filter with elimination singular point to computing cross-correlation result, after this, can be by the absolute displacement matrix that superposes by column according to filtered relative displacement array.Obtain, after absolute displacement matrix, need to strengthening displacement signal, therefore reach reinforced effects by matched filter.
Start with and ask for strain by displacement array, first absolute displacement being done to 5 strains based on method of least square estimates, the result that 5 least squares line fittings obtain is point slope form, and wherein straight slope is central point strain, and it is in 375 × 300 strain matrix that slope is deposited in to a size.
Interested regional depth is 2.5cm-4.5cm, corresponding to the 100-260 point of every string in matrix, in this section of region, find maximin, then carry out least squares line fitting and try to achieve shearing wave spread speed Vs, rule of thumb formula can be tried to achieve elastic modelling quantity again, and formula is:
E=3 ρ V
s 2wherein, ρ is tissue density.
Fig. 7 shows the two-dimensional ultrasonic image of liver in the actual use procedure of above-mentioned ultrasonic elastograph imaging system, and wherein, white lines represent liver area to be detected, and white box represents ultrasound transducer array 130 focal positions.
Fig. 8 shows the strain image over time of the white lines correspondence position of Fig. 7, and wherein, vertical coordinate represents the liver degree of depth, abscissa express time, and the slope of black lines represents the spread speed of shearing wave in hepatic tissue.
The method of the ultrasonic image-forming system of above-mentioned elasticity measurement and measurement biological tissue elasticity can obtain two-dimensional ultrasonic image and the tissue elasticity information organized simultaneously, improves clinical diagnosis accuracy; Probe can be realized accurately location under two-dimensional ultrasonic image guiding, low-frequency oscillation driving device and ultrasound transducer array are relatively independent, ultrasound transducer array can't move along with low-frequency oscillation driving device, even if ultrasound transducer array is because small movements has occurred low-frequency oscillation driving device, computing in the time carrying out strain estimation also can be offset the displacement that ultrasound transducer array small movements causes, therefore need not consider bit shift compensation, improve convenience and accuracy that tissue elasticity is measured, reduced the difficulty of processing.
The method of the ultrasonic image-forming system of above-mentioned elasticity measurement and measurement biological tissue elasticity, can obtain intuitively biological tissue, structural information that organ is detailed by the ultrasonic two dimensional image of biological tissue, in actual Transient elastography testing process, can also assist and guide the accurate location of probe and imaging surveyed area, and then the clinical diagnosis that is ultra sonic imaging in conjunction with elastic information provides more comprehensively foundation, thereby improve the accuracy of diagnosis and perspective.
The above embodiment has only expressed several embodiment of the present invention, and it describes comparatively concrete and detailed, but can not therefore be interpreted as the restriction to the scope of the claims of the present invention.It should be pointed out that for the person of ordinary skill of the art, without departing from the inventive concept of the premise, can also make some distortion and improvement, these all belong to protection scope of the present invention.Therefore, the protection domain of patent of the present invention should be as the criterion with claims.
Claims (12)
1. a ultrasonic image-forming system for elasticity measurement, is characterized in that, comprises probe, supersonic imaging device, control and blood processor and display device;
Described probe comprises:
Low-frequency oscillation driving device, for generation of the shearing wave that vibrates and form the propagation from body surface to organization internal;
Ultrasound transducer array, for launching ultrasonic signal to tissue, and tissue receiving ultrasound echo signal;
Supersonic imaging device, for according to loaded imaging parameters, drives described ultrasound transducer array to launch ultrasonic signal to biological tissue, and receives and process the ultrasound echo signal from described ultrasound transducer array;
Control and blood processor, for controlling described low-frequency oscillation driving device and supersonic imaging device, process the two-dimensional ultrasonic image and the elastic information that obtain described tissue from the ultrasound echo signal of described supersonic imaging device;
Display device, for showing two-dimensional ultrasonic image and the elastic information of described tissue;
Through hole is offered in the centre position of described ultrasound transducer array, and the vibrating shaft of described low-frequency oscillation driving device, through described through hole, low frequency and amplitude vibration occurs;
Described low-frequency oscillation driving device and described ultrasound transducer array are relatively independent, and ultrasound transducer array can't move along with low-frequency oscillation driving device.
2. the ultrasonic image-forming system of elasticity measurement according to claim 1, is characterized in that, described ultrasound transducer array comprises multiple ultrasonic transducer array element.
3. the ultrasonic image-forming system of elasticity measurement according to claim 2, is characterized in that, described through hole and described vibrating shaft match.
4. the ultrasonic image-forming system of elasticity measurement according to claim 2, is characterized in that, the length that described vibrating shaft stretches out through described through hole is 0.5～1.5 millimeter.
5. the ultrasonic image-forming system of elasticity measurement according to claim 1, is characterized in that, described low-frequency oscillation driving device is audio oscillator or motor.
6. the ultrasonic image-forming system of elasticity measurement according to claim 1, is characterized in that, described ultrasound transducer array is any one in linear array ultrasonic transducer, protruding battle array ultrasonic transducer or phase array transducer.
7. the ultrasonic image-forming system of elasticity measurement according to claim 1, is characterized in that, described supersonic imaging device comprises ultrasound emission module, ultrasonic receiver module and transmitting receiving key circuit;
Described ultrasound emission module is used for driving ultrasound transducer array transmitting ultrasonic signal;
Described ultrasonic receiver module is for receiving and process the ultrasound echo signal of described ultrasound transducer array;
Described transmitting receiving key circuit is for isolated high-voltage.
8. the ultrasonic image-forming system of elasticity measurement according to claim 1, it is characterized in that, described control and blood processor are also for the control of the Oscillation Amplitude to described low-frequency oscillation driving device, frequency, time, the parameter control of ultra sonic imaging is provided, and processes the ultrasound echo signal from described supersonic imaging device.
9. the ultrasonic image-forming system of elasticity measurement according to claim 8, it is characterized in that, described supersonic imaging device loads the imaging parameters that described control and blood processor provide, be used for driving described ultrasound transducer array transmitting ultrasonic signal, receive and process described ultrasound transducer array ultrasound echo signal and carry out wave beam and synthesize.
10. the ultrasonic image-forming system of elasticity measurement according to claim 9, it is characterized in that, the ultrasound echo signal of described supersonic imaging device after wave beam is synthetic enters described control and blood processor, obtains the Real-time Two-dimensional ultrasonoscopy of tissue through the processing of described control and blood processor.
Measure the method for biological tissue elasticity, comprise the steps: for 11. 1 kinds
Utilize the Real-time Two-dimensional ultrasonoscopy of biological tissue to position, determine biological tissue region to be detected;
Control the generation of low-frequency oscillation driving device and vibrate and form the shearing wave from body surface to described biological tissue internal communication, induce described biological tissue that miniature deformation occurs;
Utilize the each a part of ultrasonic transducer array element in vibrating shaft left and right, according to controlling and the high pulse repetition frequency transmitting ultrasonic signal of the delay parameter that provides of blood processor and 1kHz～10KHz receive ultrasound echo signal, described ultrasound echo signal synthesizes the ultrasonic signal sequence of formation along vibrating shaft center position by wave beam;
Utilize elastogram algorithm process and calculate described ultrasonic signal sequence the elastic information that obtains biological tissue region to be detected;
Show the elastic information in described biological tissue region to be detected;
Through hole is offered in the centre position of described ultrasound transducer array, and the vibrating shaft of described low-frequency oscillation driving device, through described through hole, low frequency and amplitude vibration occurs;
Described low-frequency oscillation driving device and described ultrasound transducer array are relatively independent, and ultrasound transducer array can't move along with low-frequency oscillation driving device.
12. elastograph imaging methods according to claim 11, the described step of utilizing elastogram algorithm process and the described ultrasonic signal sequence of calculating to obtain the elastic information in biological tissue region to be detected comprises:
Described ultrasonic signal sequence is carried out to filtering;
Calculate and propagate by shearing wave the displacement of tissue causing according to described filtered ultrasonic signal sequence;
Described displacement of tissue is carried out to smothing filtering and matched filtering;
According to the strain of described displacement of tissue computation organization;
Organize strain to calculate shearing wave spread speed in described biological tissue by described;
Calculate the elastic modelling quantity of described biological tissue according to shearing wave spread speed and empirical equation in described biological tissue.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201110222813.1A CN102283679B (en) | 2011-08-04 | 2011-08-04 | Ultrasonic imaging system for elasticity measurement and method for measuring elasticity of biological tissue |
| PCT/CN2012/079668 WO2013017105A1 (en) | 2011-08-04 | 2012-08-03 | Ultrasonic imaging system and method for measuring elasticity of biological tissues |
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Effective date of registration: 20160127 Address after: 102200, Beijing Changping District science and Technology Park, super Road, No. 37 Patentee after: Lepu (Beijing) Medical Equipment Co.,Ltd. Address before: 1068 No. 518055 Guangdong city in Shenzhen Province, Nanshan District City Xili University School Avenue Patentee before: Shenzhen Institutes of Advanced Technology, Chinese Academy of Science |