CN103767733A - Estimation method for RF (radio frequency) volume data in three-dimensional ultrasonic elastography of free hand - Google Patents
Estimation method for RF (radio frequency) volume data in three-dimensional ultrasonic elastography of free hand Download PDFInfo
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Abstract
The invention discloses an estimation method for RF (radio frequency) volume data in the three-dimensional ultrasonic elastography of a free hand. According to the method, on the basis that uncompressed and compressed RF frame sequences are collected, two pieces of RF volume data can be constructed according to the position of a scanned area; each RF signal sampling point of the uncompressed RF frame sequence is traversed; the point is mapped to uncompressed Volume via coordinate transformation; a voxel on the adjacent position is subjected to amplitude interpolation; each RF signal in the Volume is estimated via amplitude information by combining with the frequency and the transmission distance of the signal; each RF signal is subjected to low-pass filtering processing to finally obtain the uncompressed RF volume data; the compressed RF frame sequence is traversed by the same operation to obtain the compressed RF volume data by calculation. According to the estimation method for the RF volume data from the RF frame sequence, the obtained RF volume data can be simply and directly used for calculating the three-dimensional ultrasonic elastography, and the method is suitable for the three-dimensional ultrasonic elastography of the free hand under various complex scanning situations.
Description
Technical field
The present invention relates to computer-aided medical science technical field of imaging, particularly the method for estimation of ultrasonic radio frequency (RF) signal volume data in a kind of freedom-arm, three-D ultrasonic elastograph imaging.
Background technology
Medical ultrasound diagnosis is the important component part of modern medicine image, in the pathological diagnosis of many tissues (such as heart, liver, breast, superficial tissue etc.) of the person, has very large reference value.The quality of human body soft tissue changes conventionally and its pathological process close relation, and in the time that pathological changes occurs tissue, obvious change can occur the feature such as hard soft degree or elasticity size of tissue.
The elastic information of biological tissue has important reference value for the diagnostic procedure of disease.But, what the traditional medicine image mode including x-ray imaging, ultra sonic imaging (US), nuclear magnetic resonance (MRI), computed tomography (CT) etc. obtained is the attribute such as density and thickness of tissue, and the information of the basic mechanical attribute of this tissue of elasticity all can not be directly provided.Clinically; pathological changes (such as cancer) be organized in pathological changes when early stage the attribute such as density and thickness with organize normally very close; so adopt above imaging pattern to be all difficult to detect early stage pathological changes; and fast-developing Ultrasonic Elasticity Imaging (Elastography) in recent years; carry out imaging by obtaining related organization's elastic information; early lesion can be detected in time, made up the deficiency of traditional medicine image mode, there is important clinical value and wide application prospect.
Its ultimate principle of ultrasonic elastograph imaging is for applying an inside (comprising self) or outside, dynamic or static state/quasi-static excitation to a certain tissue; Under the physical condition such as Elasticity, biomechanics, tissue will produce a response, the distribution of for example displacement, strain and speed; Utilize Digital Signal Processing and Digital image technology, estimate the parameter such as displacement, strain of organization internal, thereby indirectly or directly reflect the difference of the mechanical attributes such as its elastic modelling quantity.
Two-dimensional ultrasonic image can react the situation in current organization cross section well, but the ultrasonic examination of 2D also has some shortcomings part, the Heuristics that 2D ultrasonic examination depends on diagnosis person is controlled the movement of ultrasonic probe, the image obtaining also only can react the information when starting section, and the 3D shape of examine position tissue (such as the solid geometry shape of focus) can only depend on diagnosis person's the imagination and can not show intuitively; 2D ultrasonic examination is difficult to the plane of delineation to navigate to the particular location in organ, is also difficult to obtain the image of organ particular cross section; In 2D ultra sonic imaging, computed range and volume depend on the formula of human organ approximate geometry, also depend on the visual angle of 2D image.From the angle quantizing and the angle that facilitates follow-up study, 2D is ultrasonic is a kind of very poor imaging pattern, and 3D imaging pattern has three-dimensional directly perceived demonstration, is convenient to measure, can obtain advantages such as organizing arbitrary section attribute information, can be good at overcoming the restriction of 2D imaging pattern.
What three-D ultrasonic elastogram obtained is the three-dimensional elastic modulus information of tissue.Three-D ultrasonic elastogram process mainly comprises obtaining of RF volume data, organizes the calculating of strain, the several steps of demonstration of 3D image reconstruction and 3-D view.Wherein, it is a vital step that RF volume data is obtained, and before and after compression, the matching of RF volume data will directly determine the correctness of strain result of calculation.The data capture method of 3-D supersonic imaging can be divided into two kinds: 1, adopt one dimensional linear array probe to obtain 2D sequence image, 2D image sequence is reconstituted to 3-D view volume data; 2, adopt two-dimensional array probe directly to obtain 3-D view volume data.Wherein adopt one dimensional linear array probe to obtain 2D sequence image and conventionally have free arm (free-hand) scanning, two kinds of scan modes of Mechanical Driven scanning; In the time adopting free arm scanning, a kind of positioner (acoustics location, optical alignment or electromagnetic locator etc.) need to be fixed on ultrasonic probe to the spatial positional information of document image in the time gathering each two field picture.
For the three-D ultrasonic elastogram of free arm scanning, in the time of image data, operator need to hold probe and be adjacent to artificial skin surface and move the RF sequence of data frames before a segment distance collection compression with certain speed, and then with probe, the tissue at same position is applied and keep certain pressure again to move the RF sequence of data frames after a segment distance collection is compressed with same speed.In the time of calculating elastic image, according to calculating elastic image with the RF frame of the rear coupling of compression before the data searching compression of twice collection, several elastic images are carried out to three-dimensional reconstruction demonstration.The thought of said method is that two-dimension elastic figure computational methods are expanded to a dimension simply to three-dimensional, its prerequisite be while gathering RF sequence of data frames before and after compression, need guarantee probe vertical in tissue surface pop one's head in simultaneously rate travel and direction identical, but the method has significant limitation in practical operation, this be because:
1, may run-off the straight or deflection in probe moving process;
2, when compress tissue scans, be difficult to guarantee that probe applied pressure is even, the direction of exerting pressure vertically;
3, probe is difficult to guarantee that rate travel is identical in move for twice front and back, and moving direction is identical.
In free arm scanning, above-mentioned three kinds of situations belong to FAQs, if operator does not have good experience, the RF frame sequence that compresses forward and backward collection will be difficult to coupling, and then cause follow-up organizing in time shift estimation and strain calculating to occur larger error, finally obtain three dimensional elasticity result and actual differing greatly.Therefore, for the common operator who there is no too much experience, the RF frame sequence that how to utilize free arm scan method to collect in the ordinary course of things, calculating correct tissue three-dimensional elastic image is a urgent problem.
Summary of the invention
The shortcoming that the object of the invention is to overcome prior art, with not enough, provides the method for estimation of RF volume data in a kind of freedom-arm, three-D ultrasonic elastograph imaging.
Object of the present invention is achieved through the following technical solutions:
In freedom-arm, three-D ultrasonic elastograph imaging, the method for estimation of RF volume data, comprises the steps:
(1) build former and later two RF data of compression Volume, determine position and the size of two Volume;
(2) travel through each sampled point that compresses each the RF signal in front RF frame sequence, this point is mapped in the front Volume of compression through Coordinate Conversion, its neighboring voxel is carried out to amplitude interpolation; For the RF frame sequence after compression, adopting uses the same method carries out interpolation to compressing rear RF volume data;
(3) interpolation complete after, for each " RF signal " in RF volume data, utilize the amplitude of each point on this " RF signal " and the frequency of signal, propagation distance, estimate an approximate real RF signal;
(4) the RF signal that in Volume, each estimates is carried out to low-pass filtering treatment, finally obtain RF volume data.
Preferably, in step (1), the position of the forward and backward RF data of compression Volume and the position range of the RF frame that size obtains according to scanning that build are determined, the upper surface of Volume will be positioned at the top of the locus of all RF frames that collect, the region of common factor mutually after the area of space that Volume region will comprise RF frame sequence place before compression and compression; Determine the voxel number of Volume in length direction according to the number of unit length pixel in RF frame, determine the size of Volume.
Preferably, the position of the forward and backward RF data of the compression of structure Volume and size are all identical.
Preferably, in step (2), first whole Volume is carried out to amplitude interpolation; When the starting point of a certain RF signal of a certain frame in traversing RF frame sequence, calculate the analytic signal of this RF signal, remember that this RF signal is rf=FS
i,j, FS
i,jthe j article of RF signal that represents i frame in frame sequence frame sequences, its analytic signal is a (t)=s (t) e
j φ (t), amplitude is s (t), phase place is φ (t).
Preferably, when the amplitude of carrying out interpolation, i sampled point of RF signal is mapped to a bit in Volume, take this point as the centre of sphere, R is radius, and value is assigned to each tissue points in spheroid, when a tissue points is asked the average of summation during by assignment repeatedly, when a tissue points once all not out-of-date by assignment, by the average of the range value of its adjacent voxels to its assignment.
Preferably, contiguous voxel is weighted to assignment to centre of sphere inverse distance as weight.
Preferably, in step (3), the estimation of RF signal, according to the amplitude of the RF volume data Volume obtaining after interpolation each " RF signal " and the frequency of signal, propagation distance, recalculates actual RF signal with RF signal approximation formula; The initial phase Φ of RF signal that compresses forward and backward Volume correspondence position is identical.
Preferably, in step (3), the estimation of RF signal, each sampled point on RF signal is not carried out to phase estimation, but estimate take a sinusoidal period or half sinusoidal period as unit according to RF signal frequency and sample rate, in carrying out phase estimation, only need calculate the starting point phase place of each cycle or half period.
Preferably, in step (4), build a FIR low pass filter, each RF signal of estimating is carried out to low-pass filtering treatment, the artificial high-frequency information of introducing of filtering, thus obtain final RF volume data.
The present invention has following advantage and effect with respect to prior art:
(1) in freedom-arm, three-D ultrasonic elastograph imaging, a kind of general interface is provided between the RF frame sequence that the present invention is equivalent to obtain in scanning and calculating elastic image, this interface can the nonstandard data acquisition modes of masking operation person, and the RF frame sequence obtaining by acquisition mode lack of standardization can well be calculated for follow-up elastic image.
(2) proposition of novelty of the present invention a kind of RF signal estimation method, by each sampled point on a RF signal is carried out to amplitude interpolation, utilize amplitude, frequency, velocity of wave, the information estimators such as propagation distance go out the waveform of RF signal, then by the high fdrequency component of low pass filter filtered signal, thereby estimate approximate real RF signal.
Accompanying drawing explanation
Fig. 1 is flow chart of the present invention;
Fig. 2 is the main use scenes schematic diagram of the present invention;
Fig. 3 (a) is position and the size of determining the front RF data Volume of compression according to RF frame sequence;
Fig. 3 (b) is position and the size of determining the rear RF data Volume of compression according to RF frame sequence;
Fig. 4 is that traversal is to a sampled point that compresses certain RF signal in a certain frame in front RF frame sequence;
Fig. 5 carries out amplitude interpolation and phase estimation to the voxel in Volume;
Fig. 6 is three RF signals of adjacent position;
Fig. 7 estimates the 2nd bars according to the 1st, 3 bars in Fig. 6, and upper part is actual signal, lower part
For the signal estimating.
The specific embodiment
Below in conjunction with embodiment and accompanying drawing, the present invention is described in further detail, but embodiments of the present invention are not limited to this.
Embodiment
As shown in Figure 1 and Figure 2, in freedom-arm, three-D ultrasonic elastograph imaging, the method for estimation of RF volume data, comprises the steps:
(1) build former and later two RF data of compression Volume, determine position and the size of two Volume;
(2) travel through each sampled point that compresses each the RF signal in front RF frame sequence, this point is mapped in the front Volume of compression through Coordinate Conversion, its neighboring voxel is carried out to amplitude interpolation; For the RF frame sequence after compression, adopting uses the same method carries out interpolation to compressing rear RF volume data;
(3) interpolation complete after, for each " RF signal " in RF volume data, utilize the amplitude of each point and the frequency of signal on this " RF signal ", propagation distance, estimates an approximate real RF signal;
(4) the RF signal that in Volume, each estimates is carried out to low-pass filtering treatment, finally obtain RF volume data.
As shown in Fig. 3 (a) and Fig. 3 (b), under normal circumstances, the RF frame sequence that free arm collects can not be the arrangement of parallel rule, but there is angle rotation and frame density difference etc. complicated situation, in this case, before compression, after RF frame sequence and compression, RF frame sequence is difficult to coupling, therefore can not be directly used in elasticity number and calculate; The present invention can utilize these RF frame sequences, go out a regular RF data volume (Volume) by Interpolate estimation, make to compress front Volume each RF signal can with compression after Volume in each RF signal well mate, thereby utilize former and later two Volume of compression directly to carry out calculating elastic image.Because the computational methods of Volume after compression are identical with Volume computational methods and process before compression with process, therefore, only to compress front Volume as example, concrete implementation step is as follows:
(1) determine position and the size of compressing front Volume.As shown in Fig. 3 (a), according to the three-dimensional coordinate (X of each pixel in each frame in RF frame sequence before compression
i, Y
i, Z
i) obtain the scope [X at three coordinate axess of RF frame sequence
min, X
max], [Y
min, Y
max], [Z
min, Z
max]; Equally as shown in Figure 3 (b), ask for the scope of the rear RF frame sequence of compression on coordinate axes, get common factor part, obtain the coordinate range [X partly that occurs simultaneously
1 min, X
1 max], [Y
1 min, Y
1 max], [Z
1 min, Z
1 max]; Find the minima on y direction of principal axis in all RF frames, the upper surface using this minima as Volume, object is exactly to allow Volume can completely enough cover the top of all RF frames.Determine behind the position of Volume, according to x in RF frame, the number of y axle unit length pixel determines that Volume is at x, y, the voxel number in z direction, the i.e. size of definite Volume.
(2) voxel in Volume is carried out to amplitude interpolation.Traversal is compressed each RF signal of each frame in front RF frame sequence, obtains analytic signal a (t)=s (t) e of this RF signal
j φ (t)obtain amplitude s (t), then travel through each sampled point of this RF signal, as shown in Figure 4, this sampled point rf (i) is carried out to coordinate transform, if the point after conversion is not in Volume, abandon it, otherwise, find take this point as the centre of sphere, R=1 is the voxel in the ball of radius, crosses the centre of sphere perpendicular to the sectional view of x axle as shown in Figure 5; Wherein, A point is the initial sampled point of a certain RF signal in a certain frame, B point is mapped to Volume mid point for traveling through to certain 1 rf (i) in RF signal after coordinate transform, the range value of current point in RF signal is assigned to all voxels in ball, if voxel is by assignment repeatedly, record by the number of times of assignment and the value composed add and, average.
(3) estimate RF signal.Obtain, after the range value of every " RF signal " in Volume, then estimating the phase place of RF signal.As shown in Figure 5, the axial string discrete point of the y of Volume is stray RF signal to be estimated; The speed c of known sound wave in tissue, frequency is f
0, propagation distance is x (t), gets initial phase Φ=0, substitution rf=s (t) cos(φ+2 π f
0in x (t)/c), just can estimate a RF signal.It should be noted that initial phase Φ can set arbitrarily, but need the initial phase of the RF signal that guarantees the forward and backward correspondence position of compression (matching) identical.Fig. 6 is three RF signals of adjacent position, and with the 1st, 3 bars are estimated the 2nd bars, and as shown in Figure 7, Fig. 7 top is divided into real the 2nd article of RF signal to result, and bottom is divided into the 2nd article of RF signal estimating.
(4) RF signal is carried out to low-pass filtering treatment.According to the frequency of RF signal and sample rate, design FIR wave filter, carries out low-pass filtering treatment to each the RF signal estimating in Volume, obtains final RF volume data.
Above-described embodiment is preferably embodiment of the present invention; but embodiments of the present invention are not restricted to the described embodiments; other any do not deviate from change, the modification done under spirit of the present invention and principle, substitutes, combination, simplify; all should be equivalent substitute mode, within being included in protection scope of the present invention.
Claims (9)
1. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging, is characterized in that, comprises the steps:
(1) build former and later two RF data of compression Volume, determine position and the size of two Volume;
(2) travel through each sampled point that compresses each the RF signal in front RF frame sequence, this point is mapped in the front Volume of compression through Coordinate Conversion, its neighboring voxel is carried out to amplitude interpolation; For the RF frame sequence after compression, adopting uses the same method carries out interpolation to compressing rear RF volume data;
(3) interpolation complete after, for each " RF signal " in RF volume data, utilize the amplitude of each point on this " RF signal " and the frequency of signal, propagation distance, estimate an approximate real RF signal;
(4) the RF signal that in Volume, each estimates is carried out to low-pass filtering treatment, finally obtain RF volume data.
2. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 1, it is characterized in that, in step (1), the position of the forward and backward RF data of compression Volume and the position range of the RF frame that size obtains according to scanning that build are determined, the upper surface of Volume will be positioned at the top of the locus of all RF frames that collect, the region of common factor mutually after the area of space that Volume region will comprise RF frame sequence place before compression and compression; Determine the voxel number of Volume in length direction according to the number of unit length pixel in RF frame, determine the size of Volume.
3. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 1 and 2, is characterized in that, position and the size of the forward and backward RF data of the compression Volume of structure are all identical.
4. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 1, is characterized in that, in step (2), first whole Volume is carried out to amplitude interpolation; When the starting point of a certain RF signal of a certain frame in traversing RF frame sequence, calculate the analytic signal of this RF signal, remember that this RF signal is rf=FS
i,j, FS
i,jthe j article of RF signal that represents i frame in frame sequence frame sequences, its analytic signal is a (t)=s (t) e
j φ (t), amplitude is s (t), phase place is φ (t).
5. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 4, it is characterized in that, when the amplitude of carrying out interpolation, i the sampled point rf (i) of RF signal is mapped to a bit in Volume, take this point as the centre of sphere, R is radius, s (i) value is assigned to each tissue points in spheroid, when a tissue points is asked the average of summation during by assignment repeatedly, when a tissue points once all not out-of-date by assignment, by the average of the range value of its adjacent voxels to its assignment.
6. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 4, is characterized in that, contiguous voxel is weighted to assignment to centre of sphere inverse distance as weight.
7. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 1, it is characterized in that, in step (3), the estimation of RF signal, according to the amplitude of the RF volume data Volume obtaining after interpolation each " RF signal " and the frequency of signal, propagation distance, with RF signal approximation formula rf=s (t) cos(φ+2 π f
0x (t)/c) recalculates actual RF signal; The initial phase Φ of RF signal that compresses forward and backward Volume correspondence position is identical.
8. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 1, it is characterized in that, in step (3), the estimation of RF signal, each sampled point on RF signal is not carried out to phase estimation, but estimate take a sinusoidal period or half sinusoidal period as unit according to RF signal frequency and sample rate, in carrying out phase estimation, only need calculate the starting point phase place of each cycle or half period.
9. the method for estimation of RF volume data in freedom-arm, three-D ultrasonic elastograph imaging according to claim 1, it is characterized in that, in step (4), build a FIR low pass filter, each RF signal of estimating is carried out to low-pass filtering treatment, the artificial high-frequency information of introducing of filtering, thus final RF volume data obtained.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104000622A (en) * | 2014-05-28 | 2014-08-27 | 华南理工大学 | Multiple-free-scanning three-dimensional ultrasound quasi-static imaging method |
| CN104706385A (en) * | 2015-01-06 | 2015-06-17 | 华南理工大学 | Ultrasound elastic wide view imaging method and device |
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Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104000622A (en) * | 2014-05-28 | 2014-08-27 | 华南理工大学 | Multiple-free-scanning three-dimensional ultrasound quasi-static imaging method |
| CN104000622B (en) * | 2014-05-28 | 2015-11-04 | 华南理工大学 | The ultrasonic quasistatic elastograph imaging method of a kind of multiple free scanning three-dimensional |
| CN104706385A (en) * | 2015-01-06 | 2015-06-17 | 华南理工大学 | Ultrasound elastic wide view imaging method and device |
| CN104706385B (en) * | 2015-01-06 | 2017-06-20 | 华南理工大学 | A kind of Ultrasonic elasticity wide-scene imaging method and device |
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