CN106780329B - A kind of plane of ultrasound wave imaging method based on the transformation of anti-perspective plane - Google Patents
A kind of plane of ultrasound wave imaging method based on the transformation of anti-perspective plane Download PDFInfo
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Abstract
The invention discloses a kind of plane of ultrasound wave imaging methods based on the transformation of anti-perspective plane, comprising the following steps: (1) acquires data；(2) data prediction: plane transformation is utilized, the imaging point first imaging point on former imaging plane being transformed in new plane, and delay time is carried out according to the imaging point in new plane revised delay time is calculated, then collectiong focusing is carried out to the imaging point on former imaging plane using synthetic aperture focusing technology further according to revised delay time, obtains the value of each imaging point on former imaging plane；(3) Data Post: envelope detected, log-compressed and grey scale mapping are successively carried out, plane of ultrasound wave image is finally obtained.The present invention is improved by the calculation to crucial delay time, and is matched with synthetic aperture focusing technology, be can effectively solve the problem that the not high problem of plane wave image quality compared with prior art, is effectively improved the imaging resolution of plane of ultrasound wave.
Description
Technical field
The invention belongs to high-resolution ultrasound technical field of imaging, are become more particularly, to one kind based on anti-perspective plane
The plane of ultrasound wave imaging method changed.
Background technique
Ultrasound detection has many advantages, such as that directive property is good, cheap, harmless, equipment is easy to carry, therefore, with super
Sound wave replaces ray to carry out irradiation object as the detection technique of emission source, and the researchers for being increasingly becoming applications of ultrasound field chase after
One of fresh target asked.
Plane wave imaging only needs primary transmitting that can complete the imaging of entire area-of-interest, therefore is a kind of quickly super
The ideal style of acoustic imaging, however compared with the multiple transmitting focusing of traditional ultrasonic imaging, plane wave is due in its emission process
Lack focusing, so that the picture quality resolution ratio only obtained by receiving focusing is low, poor contrast.
Currently, the method for improving plane wave image quality both at home and abroad has very much, such as change the deviation angle of plane wave, it is emerging to feeling
The region Multiple-Scan of interest, then echo data is averagely rebuild.Also by Fourier transform, the sky of array signal is obtained
Between frequency spectrum, rebuild using the self adaptive imaging method of broad sense coherence factor.These methods help to improve the resolution of image
Rate and contrast, but also have respective advantage and disadvantage, image taking speed is reduced on the basis of image quality improves.
Summary of the invention
Aiming at the above defects or improvement requirements of the prior art, it is flat based on anti-perspective that the purpose of the present invention is to provide one kind
The plane of ultrasound wave imaging method of face transformation, wherein improved by the calculation to crucial delay time, and with conjunction
It is matched at aperture focusing technology, can effectively solve the problem that the not high problem of plane wave image quality compared with prior art, effectively
The imaging resolution of plane of ultrasound wave is improved, and this method processing speed is fast, it is only necessary to which the transmitting of a plane of ultrasound wave utilizes
More array elements are acquired echo data.
To achieve the above object, it is proposed, according to the invention, provide it is a kind of based on anti-perspective plane transformation plane of ultrasound wave at
Image space method, which comprises the following steps:
(1) data are acquired:
Emit plane of ultrasound wave, the data of ultrasonic reflection are received and acquired using array element, obtains raw radar data；
(2) data prediction:
Plane where remembering imaging plane is X-Z plane；
Then plane conversion is carried out, imaging point all on primary plane { x, y, z } is all transformed into new plane by formula (1)
In { u, v, w }, corresponding each imaging point in new plane is obtained,
Wherein, aijFor preset conversion parameter, i=1,2,3, j=1,2,3；a33It is not zero；[dxdydz] is pre-
Coordinate translation vector between the primary plane first set and new plane the two plane origins；
Then, for any one of array element, the collectiong focusing delay of each imaging point in the new plane is calculated,
The collectiong focusing delay is corresponded with each imaging point on the primary plane；Then, it is connect according to being calculated
The delay of pinching coke carries out synthetic aperture focusing imaging to the raw radar data that each array element receives, to obtain
Take the component of each imaging point on primary plane corresponding with each array element；
(3) Data Post:
The component of each imaging point on the primary plane is weighted and averaged, to obtain each on the primary plane
The value of a imaging point；Then envelope detected, log-compressed and grey scale mapping are successively carried out again, finally obtain the imaging of plane of ultrasound wave
Image.
As present invention further optimization, in the step (2), the plane conversion is based on anti-Perspective Principles；
Preferably, the formula (1) is specially
Wherein, a33Correspond to nonlinear transformation coefficient.
As present invention further optimization, in the step (2), the formula (1) meets:
W=z+zexp (z/c)/n；
Preferably, c=1540, n=3.
As present invention further optimization, in the step (2), connecing for each imaging point in the new plane is calculated
The delay of pinching coke, the collectiong focusing delay are corresponded with each imaging point on the primary plane, specifically:
The coordinate for remembering any one of array element i is (xi,zi), the imaging point on any one of primary plane be P (x,
Z), then the collectiong focusing delay
Wherein, R' is energy converter center and the distance between the corresponding imaging point in the new plane in the new plane.
As present invention further optimization, in the step (3), the value I of each imaging point on the primary plane is full
Foot
Wherein, N is array element sum；For in the collected raw radar data of corresponding array element withMoment corresponding echo data, i.e., on the primary plane corresponding with each array element that the described step (2) obtains
The component of each imaging point；R is the distance between the imaging point on the energy converter center to the plane on the primary plane, and c is
The velocity of sound in soft tissue；Preferably, c=1540m/s.
As present invention further optimization, in the step (3),
The envelope detected, the specifically value for each imaging point on the primary plane, detect its coenvelope, extract
Low frequency component therein out, as detected material information data；
The log-compressed specifically takes logarithm to compress the detected material information data of acquisition, control compression
Data afterwards are in 40dB between 60dB；
The grey scale mapping uses Linear Mapping between 0 to 255 specifically for the compressed data of acquisition
Gray value obtains gray value data.
Using plane transformation, first original is imaged compared with prior art for contemplated above technical scheme through the invention
Imaging point in plane is transformed to the imaging point in new plane, and is calculated according to the imaging point in new plane delay time
Revised delay time is obtained, it is then flat to original imaging using synthetic aperture focusing technology further according to revised delay time
Imaging point on face carries out collectiong focusing, obtains the value of each imaging point on former imaging plane, can obtain with high-resolution
The imaging of plane of ultrasound wave, processing speed is fast, high-efficient.
Plane of ultrasound wave imaging method provided by the invention based on the transformation of anti-perspective plane, using common ultrasonic software
The plane wave data that (e.g., filedII) is generated, and for example, by SonixTouch DAQ system acquisition detected material (e.g., CIRS
Company 055A body film) reflected plane wave data, high resolution image reconstruction can be carried out；Simulation software (that is, filedII) and
Linear array probe can be used in SonixTouch DAQ system.When plane wave data carries out image reconstruction, it is assumed that ultrasound is situated between in ideal
It is propagated in matter, sonic velocity change is little, according to the echo data of generation come image reconstruction.Using SAFT (Synthetic
Apertur Focusing Technique synthetic aperture focusing technology) method, using the echo-signal received to each
Imaging point carries out collectiong focusing.It needs first to carry out plane transformation before to each imaging point focusing, calculates and prolong in new plane
The slow time calculates the value of imaging point after focusing with new delay time, then calculated result is mapped to primary plane.
Plane of ultrasound wave imaging method proposed by the present invention based on anti-Perspective Principles plane transformation, can be further improved
The resolution ratio of image improves image quality, and does not increase the complexity of software and hardware, facilitates doctor and clinically examines disease
Disconnected and treatment.It there is no the ultrasonic enterprise and research unit for grasping technique both at home and abroad at present, which does not have at home and abroad
People proposes.
Detailed description of the invention
Fig. 1 is calculating focusing delay schematic diagram after plane conversion；
Fig. 2 is corresponding simulation result, and wherein Fig. 2A is to emulate data with fieldII to carry out traditional DAS (Delay and
Sum delay superposition) rebuild, Fig. 2 B be method proposed by the present invention rebuild (that is, being focused after plane transformation) after comparison diagram；
Fig. 3 is corresponding experimental result, and wherein Fig. 3 A is CIRS company 055A body film, and Fig. 3 B, Fig. 3 C are respectively to utilize
The plane wave data of SonixTouch DAQ system acquisition carries out DAS reconstruction and method proposed by the present invention is rebuild (that is, flat
Face transformation after focus) after comparison diagram.
Specific embodiment
In order to make the objectives, technical solutions, and advantages of the present invention clearer, with reference to the accompanying drawings and embodiments, right
The present invention is further elaborated.It should be appreciated that the specific embodiments described herein are merely illustrative of the present invention, and
It is not used in the restriction present invention.As long as in addition, technical characteristic involved in the various embodiments of the present invention described below
Not constituting a conflict with each other can be combined with each other.
Plane of ultrasound wave imaging method based on anti-Perspective Principles plane transformation in the present invention is to collect ultrasonic system
Initial data carry out processing appropriate, finally rebuild ultrasound image, step includes acquisition data, data prediction, delay
Superposition, weighted average, envelope detected, log-compressed, grey scale mapping, display.
Data acquisition is emitted using plane wave, the mode of whole channel receptions, in order to obtain preferable plane wave image effect
Fruit, using the imaging of SAFT (that is, synthetic aperture focusing technique, synthetic aperture focusing technology)
Mode.Collectiong focusing is carried out to each imaging point using the echo-signal received, plane transformation is first carried out, in new plane
Delay time between upper calculating channel (between i.e. each array element).
One plane conversion is that the process of another plane is called projection mapping.According to plane conversion formula
All points can be transformed into new plane { u, v, w } on primary plane { x, y, z }, wherein aijFor conversion ginseng
Number, [dxdydz] are the coordinate translation vector between two plane origins.The present invention using non-linear plane transformation side
Formula.Plane transformation follows anti-Perspective Principles, using it is close it is small it is long-range by the way of, it is closer from origin, convert it is smaller, it is remoter from origin,
Transformation is bigger, is equivalent to and is stretched to X-Z plane, and nearlyr stretching is smaller, and remoter stretching is bigger.On primary plane it is each at
After picture point is mapped in new plane, the collectiong focusing delay that all the points are corresponded in new plane is calculated, when obtaining whole delays
Between after, further according to new delay time, calculate each receiving channel on primary plane and connect for each in the influence of the imaging point
It receives for channel, receives the echo data of array element at this point.
Hilbert transform (Hilbert-Huang Transform) is carried out after the echo data superposition that the place is had, finally
It can obtain the point data value.Rear, the matrix of available M × N is being had been calculated into each point in each imaging region
Data, M are the number for the imaging point being arranged on each channel, and N is the element number of array of linear array, carry out log-compressed, ash to data
Degree mapping, the image rebuild.
Why image resolution ratio after reconstruction improves, and is the focusing delay time because when being focused to imaging point
It is calculated in new plane, reduces the error of delay and focusing.Therefore, this plane wave imaging mode obtains tradition
The high-resolution that is unable to reach of synthetic aperture imaging method.
For example, it is X-Z plane that imaging plane, which may be selected, plane transformation can carry out X-Z plane, keep the two of transformation front and back
The coordinate origin of a plane is constant, the founding mathematical models on X-Z plane, and the formula of plane conversion can be written as
a33It is non-linear transform coefficient, anti-Perspective Principles is applied to the amplification of X-Z plane, with the side of " close small long-range "
Formula stretches Z plane, and the coordinate relationship of w and z can be designed to w=z+zexp (z/c)/n.C is the velocity of sound, and n is constant.
Select c=1540, n=3.
After have passed through plane conversion, the imaging point (x, y, z) on primary plane becomes (x, y, z+zexp in new plane
(z/c)/3), to each imaging point on primary plane, with computation delay on point of its one-to-one new plane.Such as Fig. 1 institute
Show, for imaging point P (x, z), array element i (xi,zi) caused by delay focal time be
R is that the distance between imaging point is arrived at energy converter center, and c is the soft tissue velocity of sound.C=1540m/s.
After plane transformation, the imaging point P (x, z) on primary plane becomes the F (u, w) in new plane, it is believed that
There is a virtual imaging point in new plane, therefore produces a virtual focus point.According to formula (3), delay is focused
Formula can be rewritten as
Increased part zexp (z/c)/n changes with the variation of imaging point position, and R' is in energy converter in new plane
The heart calculates every scan line for the delay time of imaging point, by delay time the distance between to imaging point in new plane
Calculating for original plane imaging point.The value of corresponding sampled point in corresponding scan line can be found by this time,
Value corresponding in all scan lines is added, the data of imaging point can be obtained, re-map on the corresponding position of original plane.Benefit
The data of imaging point can be obtained with formula (5).I is the value of imaging point.A is the data of surface sweeping line, and N is port number.By to institute
There is imaging point to be calculated, finally obtains the matrix data for being used directly for reconstruction image.
The coenvelope of envelope detected detecting signal extracts the low frequency component carried in echo-signal, i.e. testee is believed
Breath.The method for the envelope detected used in this system is Hilbert transform method, and Hilbert transform is a kind of classical seeks
The method of signal envelope, original signal will obtain the orthogonal signalling of original signal by Hilbert transform, be with original signal
Real part, the signal obtained using Hilbert transform construct complex signal as imaginary part, and the mould of this complex signal is exactly required real letter
Number envelope.
Original signal is taken denary logarithm by log-compressed, and multiplied by 20 multiple, unit is dB.Take logarithm it
The dynamic range of adjustable echo afterwards is generally adapted to 40dB or 60dB, value is got over to obtain best real time imagery effect
Small contrast is higher.Specific method is that the maximum value in signal is mapped to 60dB by taking 60dB as an example, will be smaller than peak signal
The signal of 60dB and smaller signal are mapped to 0dB.
Grey scale mapping uses simple Linear Mapping, i.e., most weak signal is proportionally mapped to 0, by strongest signal
It is mapped to 255.
Data after grey scale mapping can directly carry out the display of image.Here the imaging in MATLAB is called directly
High-resolution ultrasound plane wave image can be obtained in function.
Data Post process (e.g., envelope detected, log-compressed, grey scale mapping etc.) in the present invention is see also existing
Technology is handled, as long as can finally obtain plane of ultrasound wave image.
Certainly, except plane conversion concrete mode employed in above-described embodiment and the calculating of corresponding delay time, imaging
Outside the calculating of the value of point, plane conversion can also otherwise, either linear transformation, is also possible to other non-linear changes
It changes, for example, the n in w=z+zexp (z/c)/n formula can also take other values (such as 2,4,5), as long as plane conversion is base
In anti-Perspective Principles, by the X-Z plane where former imaging surface, (that is, closer from origin, transformation is got over by the way of " close small long-range "
It is small；It is remoter from origin, convert bigger) to stretching, origin position can remain unchanged before and after plane transformation.
As it will be easily appreciated by one skilled in the art that the foregoing is merely illustrative of the preferred embodiments of the present invention, not to
The limitation present invention, any modifications, equivalent substitutions and improvements made within the spirit and principles of the present invention should all include
Within protection scope of the present invention.
Claims (7)
1. a kind of plane of ultrasound wave imaging method based on the transformation of anti-perspective plane, which comprises the following steps:
(1) data are acquired:
Emit plane of ultrasound wave, the data of ultrasonic reflection are received and acquired using array element, obtains raw radar data；
(2) data prediction:
Plane where remembering imaging plane is X-Z plane；
Then carry out plane conversion, by formula (1) by imaging point all on primary plane { x, y, z } be all transformed into new plane u,
V, w } in, corresponding each imaging point in new plane is obtained,
Wherein, aijFor preset conversion parameter, i=1,2,3, j=1,2,3；a33It is not zero；[dxdydz] is to preset
Primary plane and new plane the two plane origins between coordinate translation vector；
Then, for any one of array element, the collectiong focusing delay of each imaging point in the new plane is calculated, it is described
Collectiong focusing delay is corresponded with each imaging point on the primary plane；Then, poly- according to the reception being calculated
Coke delay, the raw radar data received to each array element carry out synthetic aperture focusing imaging, thus obtain with
The component of each imaging point on the corresponding primary plane of each array element；
(3) Data Post:
The component of each imaging point on the primary plane is weighted and averaged, thus obtain on the primary plane it is each at
The value of picture point；Then envelope detected, log-compressed and grey scale mapping are successively carried out again, finally obtain plane of ultrasound wave image
Picture.
2. the plane of ultrasound wave imaging method as described in claim 1 based on the transformation of anti-perspective plane, which is characterized in that the step
Suddenly in (2), the plane conversion is based on anti-Perspective Principles；
The formula (1) is specially
Wherein, a33Correspond to nonlinear transformation coefficient.
3. the plane of ultrasound wave imaging method as described in claim 1 based on the transformation of anti-perspective plane, which is characterized in that the step
Suddenly in (2), the formula (1) meets:
W=z+zexp (z/c)/n；
C=1540, n=3.
4. the plane of ultrasound wave imaging method as claimed in claim 3 based on the transformation of anti-perspective plane, which is characterized in that the step
Suddenly in (2), the collectiong focusing delay of each imaging point in the new plane, the collectiong focusing delay and described Yuanping City are calculated
Each imaging point on face corresponds, specifically:
The coordinate for remembering any one of array element i is (xi,zi), the imaging point on any one of primary plane is P (x, z), then
The collectiong focusing delay
Wherein, R' is energy converter center and the distance between the corresponding imaging point in the new plane in the new plane.
5. the plane of ultrasound wave imaging method as claimed in claim 4 based on the transformation of anti-perspective plane, which is characterized in that the step
Suddenly in (3), the value I of each imaging point on the primary plane meets
Wherein, N is array element sum；For in the collected raw radar data of corresponding array element withMoment corresponding echo data, i.e., on the primary plane corresponding with each array element that the described step (2) obtains
The component of each imaging point；R is the distance between the imaging point on the energy converter center to the plane on the primary plane, and c is
The velocity of sound in soft tissue.
6. the plane of ultrasound wave imaging method as claimed in claim 5 based on the transformation of anti-perspective plane, which is characterized in that c=
1540m/s。
7. the plane of ultrasound wave imaging method as described in claim 1 based on the transformation of anti-perspective plane, which is characterized in that the step
Suddenly in (3),
The envelope detected, the specifically value for each imaging point on the primary plane, detect its coenvelope, extract it
In low frequency component, as detected material information data；
The log-compressed specifically takes logarithm to compress the detected material information data of acquisition, controls compressed
Data are in 40dB between 60dB；
The grey scale mapping uses Linear Mapping for the gray scale between 0 to 255 specifically for the compressed data of acquisition
Value, obtains gray value data.
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| CN107845082B (en) * | 2017-12-14 | 2021-10-15 | 飞依诺科技(苏州)有限公司 | Method and device for improving contrast of local area |
| CN110244305A (en) * | 2019-07-10 | 2019-09-17 | 南京信息工程大学 | A kind of emulation mode of Underwater Target Signal scattering |
| CN111580112B (en) * | 2020-06-11 | 2023-02-14 | 南京信息工程大学 | Underwater sonar sensor array imaging method based on plane waves |
| CN111965257A (en) * | 2020-08-07 | 2020-11-20 | 西南交通大学 | Space weighting optimized rapid ultrasonic plane wave imaging detection method |
| CN113436109B (en) * | 2021-07-08 | 2022-10-14 | 清华大学 | Ultrafast high-quality plane wave ultrasonic imaging method based on deep learning |
| CN117289276B (en) * | 2023-11-24 | 2024-02-27 | 航天宏图信息技术股份有限公司 | SAR image processing method and device, electronic equipment and storage medium |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0332169A1 (en) * | 1988-03-10 | 1989-09-13 | Canon Kabushiki Kaisha | Image shake detecting device |
| CN101637395A (en) * | 2008-03-13 | 2010-02-03 | 超声成像 | Method and apparatus for ultrasound synthetic imaging |
| CN103442646A (en) * | 2011-06-17 | 2013-12-11 | 松下电器产业株式会社 | Optoacoustic image pick-up system and optoacoustic image pick-up device |
| CN103455709A (en) * | 2013-07-31 | 2013-12-18 | 华中科技大学 | Super-resolution method and system for digital elevation model |
| CN104739448A (en) * | 2015-04-03 | 2015-07-01 | 深圳先进技术研究院 | Ultrasonic imaging method and device |
| CN105411626A (en) * | 2015-12-24 | 2016-03-23 | 华中科技大学 | Ultrasonic CT-based synthetic aperture imaging method and system |
-
2016
- 2016-12-07 CN CN201611113011.6A patent/CN106780329B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0332169A1 (en) * | 1988-03-10 | 1989-09-13 | Canon Kabushiki Kaisha | Image shake detecting device |
| CN101637395A (en) * | 2008-03-13 | 2010-02-03 | 超声成像 | Method and apparatus for ultrasound synthetic imaging |
| CN103442646A (en) * | 2011-06-17 | 2013-12-11 | 松下电器产业株式会社 | Optoacoustic image pick-up system and optoacoustic image pick-up device |
| CN103455709A (en) * | 2013-07-31 | 2013-12-18 | 华中科技大学 | Super-resolution method and system for digital elevation model |
| CN104739448A (en) * | 2015-04-03 | 2015-07-01 | 深圳先进技术研究院 | Ultrasonic imaging method and device |
| CN105411626A (en) * | 2015-12-24 | 2016-03-23 | 华中科技大学 | Ultrasonic CT-based synthetic aperture imaging method and system |
Non-Patent Citations (1)
| Title |
|---|
| 基于压缩感知的超声衍射层析成像研究;花少炎等;《生物医学工程学杂志》;20151025;第32卷(第5期);第975-982页 |
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