CN108852385A - A kind of x-ray imaging method and the dynamic diagosis method based on x-ray imaging - Google Patents
A kind of x-ray imaging method and the dynamic diagosis method based on x-ray imaging Download PDFInfo
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Abstract
The present invention provides a kind of x-ray imaging method, including：Original angiographic image series；Two characteristic points are chosen on a wherein frame for original angiographic image series, are extracted the clock signal of the two characteristic points and are frequency-region signal by its Fourier transformation；Signature analysis is carried out to the frequency-region signal of two characteristic points, it is poor to choose maximum at least two modulus value of the two characteristic points under identical frequency；All pixels point is traversed, Fourier's bandpass filtering treatment is done to the clock signal of each pixel on the basis of 0Hz and one of characteristic frequency, and the signal by obtaining calculates the modulation depth of each pixel；Output is using modulation depth as the image of contrast imaging parameter.In addition, additionally providing the dynamic diagosis method based on the x-ray imaging method.X-ray imaging method of the invention and the dynamic diagosis method based on x-ray imaging realize the imaging of the high s/n ratio under low x-ray dose, save and subtract shadow and interframe registration, and realize the effect of image co-registration.
Description
Technical field
When being based on the present invention relates to a kind of X-ray angiographic method more particularly to one kind based on multiframe medical image
The angiographic data processing method and dynamic diagosis method of air filter wave.
Background technique
The angiographic method of X-ray is the x-ray imaging method that background structure is removed from final image, is broadly divided into
Two kinds.First is that the side K subtraction angiography method, the method is obtained respectively slightly below and under the side the K energy of slightly above contrast agent
To the X ray image figure of sample.Then this two images is made the difference, using contrast agent to the strong absorption of X-ray on the energy of the side K
Effect can obtain containing only the blood-vessel image of contrast agent information；Second is that single energy temporal subtraction technology, on the slightly above side contrast agent K
On energy, acquisition includes the mask image of background structure.Then, inject contrast agent, then acquire the blood vessel containing contrast agent and
The image of perfused tissue.Mask image is subtracted from the image containing the blood vessel injected and perfused tissue.It just obtains in this way
Contain only the blood-vessel image of contrast agent information；Currently, general common single energy temporal subtraction technology is examined for blood vessel work-up
The disconnected, measurement of vessel position, the surgery planning of interventional therapy and biomedicine etc. research, are set by Radiation Medicine image
Standby and its follow-up data processing method realizes multiframe angiographic image.But since people's (or other living body biologicals) can not keep away
Breathing, heartbeat and the movement of other parts tissue exempted from, blood vessel are to the stress reaction of contrast agent and the vibration of external equipment
Deng directly subtracting shadow and often bring the artificial artifact for being difficult to receive.
106,999,129 101,822,545 102,103,745 102663709 A of A, CN of B, CN of A, CN of patent document CN,
It is real that 1897033 A, CN 101799918 of CN relates separately to the equipment of Technology of Digital Subtraction Angiography, the software of method in B
Existing and subsequent blood vessel enhancing, blood vessel segmentation, the elimination of motion artifacts, image co-registration of different zones angiography etc..
Wherein, method passes through additionally complete respiratory cycle image sequence of the acquisition without contrast agent in CN106999129 A
With heart beat cycle image sequence, frisket is matched by breathing phases and heartbeat phase and is full of respectively in subsequent subtracting in shadow operation
Respiration artefacts and heartbeat artifact is individually subtracted to realize the promotion of subtraction image quality in piece；Method belongs in 101822545 B of CN
A kind of image registration techniques so that Digital Subtraction operation frisket be full of piece image registration it is more accurate, thus remove movement puppet
Shadow.Method is to solve the problems, such as the elimination of motion artifacts in CN106999129 A, 101822545 B of patent CN, but complicated for operation
It is cumbersome, it is more demanding to Raw data quality.
Digital Subtraction operation is realized, it can be achieved that subtraction image with the method for computer software in CN102103745 A
Dynamic diagosis effect, but substantially digital phase detecting circuit technology is not promoted.
Method is a kind of blood vessel enhancing algorithm in 102663709 A of CN, utilizes empirical mode decomposition X-ray coronary angiography
Image is a series of intrinsic mode functions, removes ambient noise using the regularity of distribution of noise, and then select some certain layer sheets
Sign mode function is weighted construction coronary artery images, recycles the blood vessel measure function based on Hessian matrix exgenvalue
Enhance the blood vessel structure in image, to improve the visual effect of contrastographic picture；1897033 A of CN is directed to digital subtraction image not
Noise signal caused by tissue and background and target situation mixed in together can be completely eliminated, proposes that one kind is based on
The priori knowledge of blood vessel diameter and the local threshold blood vessel segmentation method of overlap partition technology, to extract the side of target blood
Method.102663709 A of CN is related to blood vessel enhancing, and 1897033 A of CN is related to blood vessel segmentation, is all based on digital phase detecting circuit behaviour
It is carried out after work, to further increase blood-vessel image quality.
It is distributed the discontinuous situation of dispersion in the blood vessel for contrast agent, it is base that CN 101799918B, which is related to image co-registration,
It is carried out after digital phase detecting circuit operation.Method in 101799918 B of CN is directed in digital phase detecting circuit, and single width subtracts shadow
Image can only represent local vascular image situation, propose a kind of number by dynamic fuzzy technology and Ridgelet transformation theory
The method for self-adaption amalgamation of subtraction image.Using the data processing method proposed in the patent document, a degree of can mention
High imaging quality.
To sum up, x-ray imaging method disclosed in these above-mentioned patent documents is based on traditional digital phase detecting circuit technology,
It is often difficult to solve following problems：
1) traditional x-ray imaging method based on digital phase detecting circuit technology is contrast agent subtraction imaging, is imitated to radiography
The undesirable image of fruit generally improves its image quality using the algorithm enhanced to geodesic structure, and algorithm is excessively complicated and promotes effect
Fruit is limited, and this algorithm is strongly depend on high dose of radiation, may lead since radiological dose is low or contrast medium concentration is too low
Contrasting effects are undesirable in the original angiographic image series caused, and then influence modulation depth, reduce the resolution ratio of image.
2) traditional x-ray imaging method based on digital phase detecting circuit technology needs to subtract shadow operation to obtain vessel graph
Picture, a crucial step are to find suitable frisket and be full of piece.But since sample inevitably moves and causes in angiographic procedure
Frisket and it is full of between piece and there is displacement, then will greatly affect the signal-to-noise ratio of imaging.The general method using interframe registration solves
This problem also needs to introduce the surface point of invasive to complete frame matching sometimes.Algorithm can greatly be increased in this way
Complexity, and picture quality is promoted limited.
3) traditional x-ray imaging method based on digital phase detecting circuit technology, selection be full of contrast agent in piece can not be complete
It is filled into all blood vessels but is partially perfused entirely.So single width contrastographic picture can only represent local vascular image situation.Doctor
It is time-consuming and laborious and be easy to fail to pinpoint a disease in diagnosis when observing multiple angiographic image series.Therefore by each width digital subtraction angiography image co-registration
Into complete image, it is allowed to be of great significance to medical aided diagnosis comprising blood vessel overall structure.But image fusion technology
It is not only complicated for operation, or even new noise can be introduced.
4) traditional x-ray imaging method based on digital phase detecting circuit technology, can not be complete for any one is full of piece
Portion finds suitable frisket, and is full of piece medium vessels and has biggish displacement.So good digital subtraction angiography can not be implemented
The dynamic diagosis of process plays.
Summary of the invention
The present invention proposes a kind of x-ray imaging method based on spatio-temporal filtering and the dynamic diagosis side based on x-ray imaging
Method is saved to realize that the high s/n ratio under low x-ray dose is imaged and subtracts shadow and interframe registration, and realize the effect of image co-registration.
To achieve the goals above, the present invention provides a kind of x-ray imaging methods, including：Step S1：With sample frequency
Fs obtains the original angiographic image series of N frame, as current angiographic image series；Step S2：In original contrastographic picture
Blood vessel characteristic point and background characteristics point are chosen on a wherein frame for sequence, extract the clock signal of the two characteristic points and will at that time
Sequential signal Fourier transformation is frequency-region signal；Step S3：Feature is carried out to the frequency-region signal of blood vessel characteristic point and background characteristics point
Analysis, successively chooses that maximum at least two modulus value of the two characteristic points under identical frequency is poor, and the i-th big modulus value difference institute is right
The frequency answered is as characteristic frequency xi*Fs/N Hz；Step S4：The institute in radiography region is traversed in current angiographic image series
There is pixel, the clock signal of each pixel is in Fu on the basis of 0Hz and one of characteristic frequency xi*Fs/N Hz
Leaf bandpass filtering treatment, and the signal by obtaining calculates the modulation depth MD of each pixeli；Step S5：Output is to modulate
Depth MDiFor the contrastographic picture of contrast imaging parameter；Wherein xi is positive integer.
The step S1 includes：Radiography object perfusion contrast agent is not perfused under the irradiation of X-ray source with contrast agent
Before being start frame acquires original angiographic image series for end frame to finishing with contrast agent perfusion.
The energy of the X-ray is higher than the ABSORPTION EDGE of the contrast agent, photon flux 109—1010photonssecond‐ 1mm‐2。
The contrast agent is non-ionic salt compounded of iodine class contrast agent, which is selected from B-15000, iodine
One of mykol, Iopromide, Ioversol, Iodixanol, cardiografin.
The dosage of the contrast agent is 100-500 microlitres, and concentration is 150-350 280mgml‐1。
Selected modulus value difference is 2-4 in the step S3, and the number of the characteristic frequency is equal to of modulus value difference
Number.
The modulation depth MD of each pixeliIt is calculate by the following formula：
Wherein, S0(x,y,t)、Sxi(x, y, t) is to do Fourier's bandpass filtering to the clock signal of each pixel respectively
The AC signal of the direct current signal and corresponding xi*Fs/N Hz frequency that are obtained after processing；
Mean(abs(Sxi(x, y, t))) it is the average value for corresponding to the absolute value of AC signal of xi*Fs/N Hz frequency；
Mean(abs(S0(x, y, t))) be direct current signal absolute value average value.
The step S4 further includes：Before all pixels point in traversal radiography region, first its each frame image is gone
It makes an uproar processing, which includes intermediate value denoising, Gauss denoising or wiener denoising.
Further, the dynamic diagosis method based on x-ray imaging that the present invention also provides a kind of, including：
Step S1 '：Using x-ray imaging method described in claim 1, characteristic frequency xi*Fs/N Hz is obtained, and is obtained
With modulation depth MDiFor the contrastographic picture of contrast imaging parameter, made corresponding to the preceding N frame as original angiographic image series
Shadow image, takes j=1；Step S2 '：The preceding N-j frames of original angiographic image series is chosen as current angiographic image series,
And characteristic frequency xi*Fs/ (N- corresponding to the current angiographic image series is calculated with the characteristic frequency that step S1 ' is obtained
j)Hz；Step S3 '：The all pixels point that radiography region is traversed in current angiographic image series, is obtained with 0Hz and step S2 '
To characteristic frequency xi*Fs/ (N-j) Hz on the basis of Fourier's bandpass filtering treatment is done to the clock signal of each pixel, and
The modulation depth MD of each pixel is calculated by obtained signali；It obtains with modulation depth MDiFor making for contrast imaging parameter
Shadow image, contrastographic picture corresponding to the preceding N-j frame as original angiographic image series；Step S4 '：When N-j is n, according to
It is secondary to play contrastographic picture corresponding to described preceding n, n+1 ..., N-1, N-2, N frame；Otherwise j+1 is updated to j and returns to step
S2’。
It is described with modulation depth MD when i is 11Contrastographic picture for contrast imaging parameter is angiographic image.
Compared with the existing x-ray imaging method based on digital subtraction technology, the X of the invention based on spatio-temporal filtering is penetrated
Line angiographic method has the characteristics that and beneficial effect.
1) the imaging parameter that the present invention uses is believed for the characteristic frequency signal of the i.e. contrast agent perfusion of modulation depth and 0 frequency direct current
Number ratio, algorithm is relatively simple, and even if due to radiological dose is low or contrast medium concentration it is too low caused by original radiography figure
Contrasting effects are undesirable in picture sequence, but its modulation depth is barely affected, so as to realize that low radiation dose is imaged, and
Traditional digital subtraction angiography method, which is compared, higher resolution ratio.According to the characteristic, the angiographic method in the present invention is not
It is appropriate only for synchrotron radiation X-ray light source and Chemical Examination Material in Hospital medical imaging device, it is similarly suitable to Laboratory X-ray light pipe light source
With.
2) it does not need to subtract shadow operation in the angiographic method in the present invention, but in a frequency domain by contrast agent perfusion
The characteristic signal of characteristic signal and biological motion noise is mutually distinguishable, so that containing only blood vessel in obtained angiographic image
Information, and the motion information of background tissues can individually be imaged.Therefore, algorithm also is substantially reduced there is no need to interframe registration
Complexity, and make the angiographic method imaging signal to noise ratio in the present invention higher, adaptively realize disappearing for motion artifacts
It removes, is more suitable for applying in the X-ray angiographic imaging with obvious motion artifacts.
3) the angiographic method imaging parameter in the present invention is modulation depth MDi, take full advantage of entire contrast agent
The information of sequence is perfused, there is no need to just can obtain the blood vessel overall structure of high quality with image fusion technology again.For radiography
Agent is distributed the discontinuous situation of dispersion in the blood vessel, can realize the effect of image co-registration automatically.
4) the present invention can provide the angiography image sequence of contrast agent perfusion process, being especially suitable for applying has obviously
In the X-ray angiographic imaging of motion artifacts.The dynamic diagosis of angiography image sequence of the invention plays, dynamic picture
Face is continuous, clear, blood vessel stability-of-path does not drift about.Because the signal of blood vessel equilibrium position is more likely to step signal and accounts for master
Lead, at non-rest position signal be more likely to class periodic signal account for it is leading.This is easy differentiation processing in a frequency domain, at frequency domain
Reason can't interfere the extraction of contrast agent perfusion information.To have periodic displacement sample medium vessels, in image
Blood vessel is also stabilized in the equilbrium position of blood vessel, without finding corresponding frisket.
Detailed description of the invention
Fig. 1 is the wherein frame image according to the original angiographic image series of one embodiment of the present of invention.
The timing letter that Fig. 2A-Fig. 2 C is correspondence 0Hz, 1*Fs/N Hz, 3*Fs/NHz of blood vessel characteristic point v as shown in Figure 1
Number figure.
Fig. 2 D- Fig. 2 F is the clock signal figure that b point as shown in Figure 1 corresponds to 0Hz, 1*Fs/N Hz, 3*Fs/N Hz.
Fig. 3 A-3B be original angiographic image series as shown in Figure 1 with MD1, MD2 be imaged parameter radiography figure
Picture.
Fig. 4 is traditional temporal subtraction angiographic image.
Specific embodiment
Below in conjunction with specific embodiment, the present invention will be further described.It should be understood that following embodiment is merely to illustrate this
The range of invention and is not intended to limit the present invention.
According to one embodiment of present invention, x-ray imaging method of the invention is based on spatio-temporal filtering, specifically includes：
Step S1：The acquisition of original radiography data.It is similar with traditional X-ray digital subtraction angiography method, to making
Contrast agent is perfused in shadow object, extremely complete with contrast agent perfusion for start frame before not being perfused with contrast agent under the irradiation of X-ray source
Finish as end frame, the original angiographic image series of tens of to the hundreds of frames of acquisition.
In the present embodiment, radiography object is experiment mice, in animal preparation process, in external carotid artery (ECA) and neck
An angiography pipe is inserted on the bifurcation of total artery (CCA), radiography region is mouse brain；Contrast agent is 180 microlitres
Concentration is 280mgIml‐1B-15000 (Iopamiro) contrast agent.Wherein, contrast agent dosage according to the biological sample of imaging, at
The picture factors such as region, x-ray photon flux can also specifically be adjusted within the scope of 100-500 microlitres, and contrast medium concentration can be according to life
The factors such as object sample tolerance level, imaging region, x-ray photon flux can also be in 150-350mgIml‐1It is specifically adjusted in range
Section.B-15000 (Iopamiro) contrast agent is a kind of non-ionic salt compounded of iodine class contrast agent, can also be by other common nonionics
One of type salt compounded of iodine class contrast agent, such as Iohexol, Iopromide, Ioversol, Iodixanol, cardiografin substitute.Blood
Pipe angiography tube injects external carotid artery (ECA), although contrast agent itself plays a part of promoting contrast, due to biological sample bone
The influence of bone or other thicker soft tissues makes contrast agent and biological sample tissue intertexture be superimposed and subtracts under shadow operation in nothing
Picture contrast is lower, or since contrast medium concentration is lower, x-ray photon flux is lower, detector detection efficient is low etc.
The influence of factor, so that collected angiographic image series contrast is relatively low；Irrigation rate is had by Baoding Lange constant flow pump
The LSP01-1A type Miniature injection pump control of limit company (Longerpump) production, injection rate are 133.3 μ ls‐1.X-ray source can
To be synchrotron radiation X-ray, laboratory X-ray machine, Chemical Examination Material in Hospital medical imaging device, X-ray source is in Shanghai in the present embodiment
The laboratory light source of synchrotron radiation light source BL13W experiment centre；Wherein the energy of X-ray is determined by used contrast agent type, one
As slightly above contrast agent ABSORPTION EDGE, in the present embodiment the energy of X-ray be 33.3keV；Photon flux is according to X-ray device
Operating status, imaging accessible radiation dosage size etc. factors determine, and improve in accessible radiation dosage range
Photon flux can correspondingly increase image quality.Photon flux is 109—1010photonssecond‐1mm‐2In range,
Photon flux is 2.38 × 1010photonssecond in the present embodiment‐1mm‐2.Detector is PCOX ray CCD (pixel size
It is 6.5 × 6.5 μm, visual field size is 13 × 13mm, PCO-TECH Inc, Germany)；The detector time for exposure is 10 milliseconds, adopts
Integrate frame per second, that is, sample frequency Fs as 100fps.
In addition, obtaining for initial data can also be made using correspondence is intercepted from traditional temporal subtraction angiographic sequence
That a part of sequence of shadow agent perfusion.
For the angiographic image series that step S1 is obtained, since contrast agent is to the absorption of X-ray, vasculature part and back
There is different timing variations feature in scape tissue part.Background tissues are a series of stationary singnal in the ideal situation, but real
In the operation of border due to inevitably breathing, heartbeat and the movement of other parts tissue, blood vessel is to the stress reaction of contrast agent
It is one group of class periodic vibration signal or other kinds of hash in timing with the reasons such as the vibration of external equipment.
Corresponding angiosomes should be ideally as the filling situation and concentration of contrast agent become due to the perfusion of contrast agent
The one group of signal changing situation and changing.It is that one group of class periodic signal is superimposed upon on a step signal in practical operation.By
This, its difference compared with background tissue signal of the signal of corresponding angiosomes is only in that blood vessel signal has more a step
Signal, this step signal correspond to the vessel information of contrast agent perfusion.
Step S2：Two characteristic points are chosen on a wherein frame for original angiographic image series, extract the two features
Point clock signal and by its clock signal Fourier transformation be frequency-region signal.
It is as shown in Figure 1 a wherein frame for original angiographic image series.In this frame of original angiographic image series
Upper to choose following two characteristic points, one chooses the angiosomes pixel being clearly located on blood vessel as blood vessel characteristic point v.Its
Two choose with the representative background tissues pixel of movement as background characteristics point b.Extract the timing letter of two characteristic point
Number, it can be found that the signal at background characteristics point b is the superposition of cyclical signal and static direct current signal.At blood vessel feature v
Signal is then similar to static direct current signal and partial periodicity Signal averaging on a step signal.Then to two extracted
Clock signal carries out Fourier frequency domain transformation using the method for Fast Fourier Transform (FFT) (FFT).
Thus obtained frequency-region signal, if sample frequency is Fs；Number of samples is identical as frame number, is set as N；Then in frequency domain
0Hz frequency corresponds to direct current (DC) signal, 1*Fs/N Hz, 2*Fs/N Hz, 3*Fs/N Hz ..., i*Fs/N Hz ... (N-1) *
The frequency of Fs/N Hz corresponds to high-frequency ac (AC) signal.Blood vessel characteristic point v corresponding modulus value at frequency i*Fs/N Hz is
Avi, i.e. the corresponding modulus value of blood vessel characteristic point v includes Av1、Av2、Av3、…Avi…AvN‐1；Background characteristics point b is in frequency i*Fs/N
Corresponding modulus value is Ab under Hzi, i.e. the corresponding modulus value of background characteristics point b includes Ab1、Ab2、Ab3、…Abi…AbN‐1。
Step S3：Signature analysis is carried out to the frequency-region signal of blood vessel characteristic point v, background characteristics point b, two characteristic points b, v exist
Modulus value difference under identical frequency changes with the variation of frequency, from big to small successively choose 2 modulus value it is poor, corresponding to frequency
Rate is as characteristic frequency.
In the present embodiment, maximum 2 frequencies of modulus value difference are only had chosen as characteristic frequency, the two characteristic frequencies
X1*Fs/N Hz=1*Fs/N Hz, x2*Fs/N Hz=3*Fs/N Hz, wherein characteristic frequency corresponding to maximum modulus value difference
It is indicated by x1*Fs/N Hz, size is 1*Fs/N Hz, corresponds to blood vessel；Characteristic frequency corresponding to secondary maximum modulus value difference by
X2*Fs/N Hz indicates that size is 3*Fs/N Hz, corresponds to the background tissues of movement.
Wherein, modulus value difference and X-ray intensity, detector time for exposure, contrast agent dosage, sample type thickness etc. are because being known as
It closes.We in practice, under sample accessible radiation dosage, the preferable original contrastographic picture of collection image quality as far as possible
Sequence, under normal circumstances, modulus value have apparent differentiable difference, about 5-20 times of modulus value.It therefore, generally also can be with
Successively modulus value difference be greater than modulus value 5 times of 2-4 modulus value it is poor corresponding frequency as characteristic frequency (the i-th big mould
Frequency corresponding to value difference is as characteristic frequency xi*Fs/N Hz), and 2 are not limited solely to, to distinguish blood vessel signal easily
And background tissue signal.The poor corresponding characteristic frequency x1*Fs/N Hz of maximum modulus value must be the best frequency of contrast agent perfusion signal
Rate, and the corresponding modulus value of blood vessel characteristic point v is necessarily greater than the corresponding modulus value of background characteristics point b under the frequency；And other features frequency
Rate often corresponds to blood vessel signal or the superposition of both of motion artifacts or non-optimal, the corresponding modulus value of blood vessel characteristic point v and
The corresponding smaller and size relation of the corresponding modulus value difference of background characteristics point b is indefinite.
In most cases, contrast agent is the continuous primary perfusion of constant concentration, therefore in original contrastographic picture sequence
In column, the signal of blood vessel characteristic point v corresponds to step signal, and characteristic frequency is 1*Fs/N Hz.If concentration becomes when contrast agent perfusion
Change perhaps has special perfusion feature off and on or in certain local special blood vessels greatly, then contrast agent perfusion is believed
Number non-step signal, blood vessel characteristic frequency is also likely to be other frequencies.
Step S4：In the case where taking i=1 or 2, all pictures in radiography region are traversed in original angiographic image series
Vegetarian refreshments is cooked Fourier's bandpass filtering treatment to the clock signal of each pixel on the basis of 0Hz and one of characteristic frequency,
Calculate the contrast imaging parameter of each pixel, i.e. modulation depth (MDi)。
It wherein, can be in traversal radiography region if many of original image of angiographic image series clutter noise
Before all pixels point, i.e., before the contrast imaging parameter for calculating every bit, denoising, example first are done to its each frame image
Such as intermediate value denoising, Gauss denoising, wiener denoising.
By taking any pixel point s (x, y) as an example, the contrast imaging parameter of the point is calculated.Firstly, taking out the timing of the pixel
Signal does Fourier's bandpass filtering treatment to the clock signal on the basis of 0Hz, x1*Fs/N Hz, x2*Fs/N Hz.Band logical filter
Signal after wave is S0(x,y,t)、Sx1(x,y,t)、Sx2(x,y,t).Wherein, S0(x, y, t) is direct current signal, Sx1(x,y,
t)、Sx2(x, y, t) is the AC signal of corresponding frequencies.For example, in the present embodiment, to blood vessel characteristic point v and background characteristics point b
Clock signal, Fourier's bandpass filtering treatment is done to the clock signal on the basis of 0Hz, x1*Fs/N Hz, x2*Fs/N Hz.
V point signal after bandpass filtering is Sv0(x,y,t)、Svx1(x,y,t)、Svx2(x, y, t), wherein S as shown in Figure 2 av0(x,
Y, t) it is direct current signal；As shown in Fig. 2 b, 2c, the AC signal of corresponding frequencies is Svx1(x,y,t)、Svx2(x,y,t).Band logical filter
B point signal after wave is Sb0(x,y,t)、Sbx1(x,y,t)、Sbx2(x, y, t), wherein as shown in Figure 2 d, Sb0(x, y, t) is
Direct current signal.As shown in Fig. 2 e, 2f, the AC signal of corresponding frequencies is Sbx1(x,y,t)、Sbx2(x,y,t).AC signal is corresponding
Contrast agent perfusion signal or background tissues motion artifacts signal.
Then, the output contrast imaging parameter for calculating the pixel is modulation depth (MDi), formula is as follows：
Mean(abs(Sxi(x, y, t))) it is the average value for corresponding to the absolute value of AC signal of xi*Fs/N Hz frequency.
Mean(abs(S0(x, y, t))) be direct current signal absolute value average value.Denominator Mean (abs (S0(x, y, t))) effect
To do normalized to the different zones of imaging.This is because due to incident X-rays inhomogeneity and contrastographic picture not
With the difference of the density in region, thickness, Elemental redistribution.The pixel of different zones has the pixel Distribution value of larger difference.Cause
The blood vessel of different zones has different contrasting effects.It is unfavorable for whole angiographic imaging.Therefore, returned with direct current signal work
One changes, and can remove the influence of the factor.
In addition, the i in step S4 can take 1 to arrive feature when the total number of the obtained characteristic frequency of step S3 is not 2
Any one number between the total number of frequency, and be not limited to take i=1 or 2.
Step S5：Output is with MD1、MD2For the contrastographic picture that parameter is imaged.
It is the contrastographic picture that parameter is imaged with MD1, MD2 as Fig. 3 a, 3b are shown in the present embodiment.It is mainly wrapped in Fig. 3 a
Containing vessel information, the corresponding i.e. x1*Fs/NHz of characteristic frequency of maximum modulus value difference is corresponded to.This part signal corresponds to blood vessel
Signal is perfused, the constituent signals intensity is 10 times of its background tissues in angiosomes pixel.Fig. 3 b is mainly the background moved
Tissue corresponds to the poor corresponding i.e. x2*Fs/N Hz of characteristic frequency of time maximum modulus value, which is mainly respiratory movement.
This example has successfully distinguished blood vessel signal and motion artifacts.
Generally, the pixel in contrastographic picture medium vessels region, due to the perfusion of contrast agent, clock signal is ideally
For step signal, main feature signal distributions characteristic frequency x1*Fs/ corresponding to maximum modulus value difference after frequency domain filtering
On N Hz, and correspondingly, the main feature of its clock signal of background area in contrastographic picture is distributed in other frequencies, this is frequently
Rate and vascular perfusion frequency have certain difference.Method in the present invention can easily distinguish contrast agent signals and background very much
The motion artifacts of tissue improve the resolution ratio of imaging to achieve the effect that inhibit noise.Therefore, in these contrastographic pictures,
General MD1For angiographic image, MD2For the high frequency motion organization chart picture of respective frequencies, such as the movement influenced by breathing
Organization chart picture, the motor tissue image influenced by jerk etc..This illustrates that the method in the present invention can be distinguished easily very much
The motion artifacts of the contrast agent signals and background tissues opened cannot be distinguished in conventional digital deshadowing technology out.As control, this example is given
Traditional temporal subtraction angiographic image is gone out as shown in figure 4, wherein the motion artifacts of contrast agent signals and background tissues are remote
It is clear in the present invention to can not show a candle to, and also cannot be distinguished and come.
In addition, the present invention also provides a kind of dynamic diagosis method based on x-ray imaging, including：
Step S1 '：I=1 is taken, using x-ray imaging method described above, obtains characteristic frequency x1*Fs/NHz, and obtain
To with MD1For the angiographic image of contrast imaging parameter, blood vessel corresponding to the preceding N frame as original angiographic image series
Contrastographic picture, and take j=1；
Step S2 '：The preceding N-j frame of original angiographic image series is chosen as current angiographic image series, and with step
The characteristic frequency that rapid S1 ' is obtained calculates characteristic frequency xi*Fs/ (N-j) Hz corresponding to the current angiographic image series；Feature
Frequency correspondingly replaces with x1*Fs/ (N-j) Hz by x1*Fs/N Hz, is the step signal because of corresponding contrast agent signals, not
Also accordingly change with its characteristic frequency in the clock signal of length.
Step S3 '：The step S4 and step S5 for repeating x-ray imaging method described above, specifically include：Current
The all pixels point in radiography region, the characteristic frequency x1*Fs/ obtained with 0Hz and current procedures S2 ' are traversed in angiographic image series
(N-j) Fourier's bandpass filtering treatment is done to the clock signal of each pixel on the basis of Hz, and the signal by obtaining calculates
The modulation depth MD of each pixel1；It obtains with modulation depth MD1For the angiographic image of contrast imaging parameter, as original
Angiographic image series preceding N-j frame corresponding to angiographic image；
Step S4 '：When N-j is n, contrastographic picture corresponding to preceding n, n+1 ..., N-1, N-2, N frame is playd in order；Otherwise
J+1 is updated to j and returns to step S2 '.Wherein n is the image frame number that contrast agent is filled into radiography region just.
Achieve that the dynamic diagosis of angiographic procedure plays in this way, dynamic menu is continuous, clear, blood vessel stability-of-path is not trembled
It is dynamic.
Above-described, only presently preferred embodiments of the present invention, the range being not intended to limit the invention, of the invention is upper
Stating embodiment can also make a variety of changes.Made by i.e. all claims applied according to the present invention and description
Simply, equivalent changes and modifications fall within the claims of the invention patent.The not detailed description of the present invention is
Routine techniques content.
Claims (10)
1. a kind of x-ray imaging method, including：
Step S1：The original angiographic image series that N frame is obtained with sample frequency Fs, as current angiographic image series；
Step S2：Blood vessel characteristic point and background characteristics point are chosen on a wherein frame for original angiographic image series, extract this
The clock signal of two characteristic points and by its clock signal Fourier transformation be frequency-region signal；
Step S3：Signature analysis is carried out to the frequency-region signal of blood vessel characteristic point and background characteristics point, successively chooses the two features
Maximum at least two modulus value of the point under identical frequency is poor, and frequency corresponding to the i-th big modulus value difference is as characteristic frequency xi*
Fs/N Hz；
Step S4：The all pixels point in radiography region is traversed, in current angiographic image series with 0Hz and one of feature
Fourier's bandpass filtering treatment, and the letter by obtaining are done to the clock signal of each pixel on the basis of frequency xi*Fs/N Hz
Number calculate the modulation depth MD of each pixeli；
Step S5：Output is with modulation depth MDiFor the contrastographic picture of contrast imaging parameter；
Wherein xi is positive integer.
2. x-ray imaging method according to claim 1, which is characterized in that the step S1 includes：Radiography object is filled
Contrast agent is infused, is that start frame is finished to contrast agent perfusion as end under the irradiation of X-ray source, before not being perfused with contrast agent
Frame acquires original angiographic image series.
3. x-ray imaging method according to claim 2, which is characterized in that the energy of the X-ray is higher than the contrast agent
ABSORPTION EDGE, photon flux 109—1010photons second‐1mm‐2。
4. x-ray imaging method according to claim 2, which is characterized in that the contrast agent is non-ionic salt compounded of iodine class
Contrast agent, the non-ionic salt compounded of iodine class contrast agent are selected from B-15000, Iohexol, Iopromide, Ioversol, Iodixanol, general shadow
One of Portugal's amine.
5. x-ray imaging method according to claim 2, which is characterized in that the dosage of the contrast agent is 100-500
Microlitre, concentration is 150-350mgIml‐1。
6. x-ray imaging method according to claim 1, which is characterized in that selected modulus value is poor in the step S3
It is 2-4, and the number of the characteristic frequency is equal to the number of modulus value difference.
7. x-ray imaging method according to claim 1, which is characterized in that the modulation depth MD of each pixeli
It is calculate by the following formula：
Wherein, S0(x,y,t)、Sxi(x, y, t) is to do Fourier's bandpass filtering treatment to the clock signal of each pixel respectively
The AC signal of the direct current signal and corresponding xi*Fs/N Hz frequency that obtain afterwards；
Mean(abs(Sxi(x, y, t))) it is the average value for corresponding to the absolute value of AC signal of xi*Fs/N Hz frequency；
Mean(abs(S0(x, y, t))) be direct current signal absolute value average value.
8. x-ray imaging method according to claim 1, which is characterized in that the step S4 further includes：In traversal radiography
Before all pixels point in region, denoising first is done to its each frame image, which includes that intermediate value denoises, Gauss is gone
It makes an uproar or wiener denoises.
9. a kind of dynamic diagosis method based on x-ray imaging, including：
Step S1 '：Using x-ray imaging method described in claim 1, characteristic frequency xi*Fs/N Hz is obtained, and is obtained to adjust
Depth MD processediFor the contrastographic picture of contrast imaging parameter, radiography figure corresponding to the preceding N frame as original angiographic image series
Picture takes j=1；
Step S2 '：The preceding N-j frame of original angiographic image series is chosen as current angiographic image series, and with step S1 '
Obtained characteristic frequency calculates characteristic frequency xi*Fs/ (N-j) Hz corresponding to the current angiographic image series；
Step S3 '：The all pixels point that radiography region is traversed in current angiographic image series, is obtained with 0Hz and step S2 '
Characteristic frequency xi*Fs/ (N-j) Hz on the basis of Fourier's bandpass filtering treatment is done to the clock signal of each pixel, and lead to
The signal crossed calculates the modulation depth MD of each pixeli；It obtains with modulation depth MDiFor the radiography of contrast imaging parameter
Image, contrastographic picture corresponding to the preceding N-j frame as original angiographic image series；
Step S4 '：When N-j is n, contrastographic picture corresponding to described preceding n, n+1 ..., N-1, N-2, N frame is playd in order；Otherwise
J+1 is updated to j and returns to step S2 '.
10. the dynamic diagosis method according to claim 9 based on x-ray imaging, which is characterized in that when i is 1, institute
It states with modulation depth MD1Contrastographic picture for contrast imaging parameter is angiographic image.
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