CN110954481B - Optimized average polarization demodulation method for catheter polarization sensitive optical coherence tomography - Google Patents

Optimized average polarization demodulation method for catheter polarization sensitive optical coherence tomography Download PDF

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CN110954481B
CN110954481B CN201911107624.2A CN201911107624A CN110954481B CN 110954481 B CN110954481 B CN 110954481B CN 201911107624 A CN201911107624 A CN 201911107624A CN 110954481 B CN110954481 B CN 110954481B
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丁振扬
刘铁根
赖天铎
朱丰裕
陶魁园
赵会硕
朱亚楠
花培栋
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Abstract

The invention relates to a catheter polarization sensitive optical coherence tomography optimized average polarization demodulation method, which comprises the following steps: adjusting all three-ring polarization controllers in the system respectively to enable the polarization of the reference light and the polarization of the input light to be balanced on two balanced detectors (H, V channels); acquiring a sample Mueller matrix; carrying out averaging processing on the obtained Mueller matrix; selecting a sample special point as a reference point, and calculating a measurement matrix by using the averaged Mueller matrix; carrying out Mueller matrix decomposition on the measurement matrix, and solving the phase delay amount by utilizing the matrix similarity relation; and (3) performing coordinate interpolation transformation on the phase retardation under the polar coordinate, and converting the polar coordinate into a Cartesian coordinate to obtain a phase retardation image, namely a polarization image, of the sample of the catheter polarization-sensitive optical coherence tomography system.

Description

Optimized average polarization demodulation method for catheter polarization sensitive optical coherence tomography
Technical Field
The invention relates to a catheter optical coherence tomography method. In particular to a polarization demodulation average denoising method for polarization-sensitive optical coherence tomography of a catheter.
Background
The catheter OCT imaging technology is a blood vessel imaging method with the highest image resolution at present, particularly the catheter PS-OCT imaging technology, can solve the medical problem that the stability of atherosclerotic plaques is difficult to judge in vivo, in real time and rapidly, and can improve the prevention and treatment effect of atherosclerotic diseases. However, the existing OCT systems have reached the level of possibly determining the properties of tissue plaques in terms of resolution, but are still insufficient in terms of tissue penetration ability, image sharpness, and accuracy of tissue plaque type determination, and it is a key direction in development of OCT systems to improve the performance of related technologies by using the PS-OCT technology.
Despite the great advances in plaque identification and diagnosis made by catheter OCT, there is still a need for new technologies that will yield further improvements in the accuracy of in vivo detection of plaque morphology and composition. Related studies have shown that tissues containing fibrous structures, such as interstitial collagen or layered arterial smooth muscle cells, exhibit birefringent effects. Lipid tissue exhibits a strong depolarizing effect. At present, the traditional OCT only provides the intensity information of tissue scattering, and the polarization characteristics of the tissue, such as birefringence effect, depolarization effect and the like, cannot be measured. If a catheter Polarization sensitive OCT (PS-OCT) system capable of detecting Polarization characteristics is developed, the accuracy of atheromatous plaque property and structure diagnosis is further improved, and the blood circulation reconstruction is correctly guided. Tsingtao et al at Tianjin university propose a similar Mueller matrix polarization calculation method (201811088259.0), which can effectively demodulate the polarization information of biological tissues, but the method lacks an averaging process and is difficult to effectively overcome the problems of depolarization, signal-to-noise ratio reduction and the like.
Disclosure of Invention
The technical problem to be solved by the invention is to provide a polarization demodulation average denoising method capable of realizing polarization demodulation of a PS-OCT image of a catheter. The technical scheme is as follows:
a catheter polarization sensitive optical coherence tomography optimized average polarization demodulation method comprises the following steps:
(1) adjusting all three-ring polarization controllers in the system respectively to enable the polarization of the reference light and the polarization of the input light to be balanced on two balanced detectors (H, V channels);
(2) sample mueller matrix acquisition, denoted by s (z), was as follows:
scanning a sample, obtaining signals H, V by respectively carrying sample information signals directly collected by two balanced detectors through numerical dispersion compensation and interpolation Fourier transform, obtaining a segmentation threshold value through autocorrelation peak searching, and segmenting the signals into four parts H1，H2，V1，V2(ii) a Sampling values of four parts corresponding to the same Z position point of a sample to form a Jones matrix of a pixel point complex signal
Figure BDA0002271794760000011
Converting the image into a Mueller matrix S (z) by using Jones matrix conversion Mueller matrix formula;
(3) and carrying out average processing on the obtained Mueller matrix, wherein the method comprises the following steps:
the mueller matrix at the z position is expressed as:
Figure BDA0002271794760000012
averaging with surrounding points using a moving average window, and expressing the averaged mueller matrix as:
Figure BDA0002271794760000021
wherein
Figure BDA0002271794760000022
I is an area contained by the selected average window, t refers to all points in the area, N is the number of points contained by the window, s is a central point of the average window, the averaging process is that the average value in the window replaces a value at the central position, the moving average window processes all data points to obtain a Mueller matrix after all the data points are averaged, and the Mueller matrix replaces an original Mueller matrix to carry out calculation;
(4) selecting a special point of a sample as a reference point, and calculating a measurement matrix by using the averaged Mueller matrix, wherein the method comprises the following steps:
determining the outer surface of the catheter or the surface of the sample as reference points, and taking the Mueller matrix writing after averaging the points
Figure BDA0002271794760000023
Will be provided with
Figure BDA0002271794760000024
And
Figure BDA0002271794760000025
operating to obtain a sampleMeasurement matrix M at z (z)ref,z)：
Figure BDA0002271794760000026
MSTIs a sample Mohler matrix, MoutMueller matrix, Q, representing the output beam path of the systemrefAn equivalent Mueller matrix representing the reference light;
(5) performing Mueller matrix decomposition on the measurement matrix, and solving the phase delay amount by utilizing the matrix similarity relation, wherein the method comprises the following steps:
will measure the matrix M (z)refAnd z) carrying out Lu-Chipman matrix decomposition, eliminating depolarization and double attenuation effects to obtain a Moeller matrix only containing double refraction:
Figure BDA0002271794760000027
wherein M isR(zref,z),
Figure BDA0002271794760000028
And
Figure BDA0002271794760000029
is a Mueller matrix comprising only birefringent components, corresponding to M (z)ref,z),MST(z),MoutAnd Qref；
By utilizing the matrix similarity relation, the phase retardation R under the polar coordinate is calculated by using a measurement Mueller matrix only containing birefringence, and the formula is as follows:
Figure BDA00022717947600000210
tr () represents the trace of the matrix;
(6) and (3) performing coordinate interpolation transformation on the phase retardation under the polar coordinate, and converting the polar coordinate into a Cartesian coordinate to obtain a phase retardation image, namely a polarization image, of the sample of the catheter polarization-sensitive optical coherence tomography system.
According to the method, a moving window averaging method is added to the measurement of the Mueller matrix on the basis of the polarization demodulation method based on the similarity of the Mueller matrix, so that the signal-to-noise ratio of the polarization demodulation signal can be remarkably improved, and the contrast of the polarization characteristic diagram is improved. Compared with the global phase average and the complex number domain average in the similar Jones matrix method, the method has the advantages that the real number operation is completely adopted in the averaging process, and the operation is simple and efficient.
Drawings
FIG. 1 is a schematic diagram of a catheter polarization-sensitive optical coherence tomography system of the present invention
FIG. 2 is a flowchart of a polarization demodulation mean denoising method for catheter polarization-sensitive optical coherence tomography according to the present invention.
FIG. 3 polarization demodulation results of chicken breast tissue
(a) Intensity image (b) treated birefringent phase retardation by the similar mueller matrix method without averaging
(c) Birefringent phase retardation processed using an optimized average semeller matrix approach
FIG. 4 polarization demodulation results of porcine myocardial tissue
(a) Intensity image (b) treated birefringent phase retardation by the similar mueller matrix method without averaging
(c) Birefringent phase retardation processed by optimized average semeller matrix method
FIG. 5 shows the polarization demodulation results of human nail tissue
(a) Intensity image (b) treated birefringent phase retardation by the similar mueller matrix method without averaging
(c) Birefringent phase retardation processed by optimized average semeller matrix method
Detailed Description
The following describes a polarization demodulation and average denoising method for polarization-sensitive optical coherence tomography in a catheter according to the present invention in detail with reference to the embodiments and the accompanying drawings.
The polarization demodulation average denoising method for the polarization-sensitive optical coherence tomography of the catheter utilizes the Mueller matrix to represent the polarization characteristics of a system and a sample, and eliminates the depolarization and double attenuation effects of the system and the sample through matrix decomposition. The noise is weakened through the averaging of the Mueller matrix, the birefringence phase delay of the sample is obtained through deducing the internal relation between the sample transmission matrix and the PS-OCT signal matrix, namely the condition that the two matrixes are similar and the traces of the similar matrixes are equal, and the polarization demodulation of the PS-OCT image of the catheter is realized.
The invention relates to a polarization demodulation average denoising method for catheter polarization-sensitive optical coherence tomography (PS-OCT), which is used for a catheter polarization-sensitive optical coherence tomography (PS-OCT) system shown in figure 1 and has the working principle that:
emergent light of a scanning light source 1 of the catheter PS-OCT system enters from a port 1 of a 1:99 optical fiber coupler 2 and is distributed to a sample arm and a reference arm from ports 2 and 3 in a ratio of 1:99 respectively. Emergent light of a port 2 of a 1:99 optical fiber coupler 2 enters a sample arm, light beams entering the sample arm enter a polarization-maintaining optical fiber 4 with the length of 18.5 meters after entering a three-ring polarization controller 3, the light beams enter a port 1 of a circulator 6, the light is emitted from the port 2 of the circulator 6, the emergent light enters an imaging guide pipe 11 through a rotating mechanism 8, the light reflected by a sample returns to the circulator 6 from the imaging guide pipe 11, and the light is emitted through a port 3 of the circulator 6. Emergent light of a port 3 of the 1:99 optical fiber coupler 2 enters a reference arm, light entering the reference arm enters a single-mode optical fiber 5 with the length of 18.5 meters, the emergent light enters a port 1 of a circulator 7, the emergent light exits from the port 2 and enters a reflective optical fiber delay line 10, reflected light enters through the port 2 of the circulator 7 and exits from the port 3 to a three-ring polarization controller 9. Emergent light of a sample arm passing through a port 3 of a circulator 6 and emergent light of a reference arm passing through a three-ring polarization controller 9 are respectively incident into a 50:50 optical fiber coupler 12 from ports 1 and 2 of the optical fiber coupler 12 to interfere, and respectively enter a three-ring polarization controller 13 and a three-ring polarization controller 14 from ports 3 and 4 in a ratio of 50:50, the emergent light is respectively incident into polarization beam splitters 15 and 16, the emergent light of the optical fiber beam splitter 15 is respectively incident into balance detectors 17 and 18 from ports 1 and 2, the emergent light of the polarization beam splitter 16 is respectively incident into the balance detectors 17 and 18 from ports 1 and 2, and electric signals of the balance detectors 17 and 18 are received by an acquisition card 19 and transmitted into a computer 20.
The light source adopts a fast scanning light source, a polarization maintaining optical fiber is adopted in the system to generate orthogonal polarization state delay, polarization diversity acquisition is carried out through a polarization beam splitter, and the length of the polarization maintaining optical fiber depends on the birefringence of the polarization maintaining optical fiber to generate phase delay equal to half of the imaging depth of the common OCT. The method ensures that the system can simultaneously present polarization diversity imaging of two orthogonal input polarization states in one image, and provides possibility for eliminating system birefringence change introduced by catheter rotation subsequently.
As shown in FIG. 2, the polarization demodulation average denoising method for catheter polarization-sensitive optical coherence tomography according to the present invention includes the following steps:
1. reference light and input light polarization adjustment
First, the system is adjusted, the three-ring polarization controller 9, the three-ring polarization controller 13 and the three-ring polarization controller 14 are respectively adjusted to make the light intensities of the reference light on the two balanced detectors 17 and 18(H, V channels) equal, and then the three-ring polarization controller 3 is adjusted to make the light intensities of the input light on the two balanced detectors 17 and 18(H, V channels) equal.
2. Sample mueller matrix acquisition
After the system is adjusted, the sample starts to be scanned, signals carrying sample information and directly collected by the two balanced detectors 17 and 18 are subjected to numerical dispersion compensation and interpolation Fourier transform respectively to obtain signals H, V, and the signals are divided into four parts H by obtaining a division threshold value through autocorrelation peak searching1，H2，V1，V2. The whole sample is regarded as being composed of isolated points, value groups of four parts corresponding to the same point of the sample form a Jones matrix of a pixel point complex signal, and the Jones matrix of the point at the z position is written
Figure BDA0002271794760000041
It is converted into a Mueller matrix S (z) by using the Jones matrix conversion Mueller matrix formula.
3. Averaging the obtained Mueller matrix
The mueller matrix at the z position can be expressed as:
Figure BDA0002271794760000042
averaging with surrounding points using a moving average window, and expressing the averaged mueller matrix as:
Figure BDA0002271794760000043
wherein
Figure BDA0002271794760000044
I is the area encompassed by the selected averaging window, t refers to all points in the area, N is the number of points encompassed by the window, s is the center point of the averaging window, the averaging process is the average value within the window instead of the value at the center position. And processing all data points by the moving average window to obtain a Mueller matrix after all the data points are averaged, and replacing the original Mueller matrix for calculation.
4. Selecting a special point of the sample as a reference point, and calculating a measurement matrix by using the averaged Mueller matrix
Let MSTIs a sample Mohler matrix, Min，MoutMueller matrix, Q, representing the optical path of the systemin，QrefRepresenting equivalent mueller matrices for the input light and the reference light, the average mueller matrix at the z position can be expressed as:
Figure BDA0002271794760000045
determining the outer surface of the catheter or the surface of the sample as reference points, and taking the average of the reference points to write a Mueller matrix
Figure BDA0002271794760000046
Then there is
Figure BDA0002271794760000047
Will be provided with
Figure BDA0002271794760000048
And
Figure BDA0002271794760000049
respectively operating to obtain a measurement matrix M (z) of the sample at the z positionref,z)：
Figure BDA00022717947600000410
5. Performing Mueller matrix decomposition on the measurement matrix, and solving the phase delay amount by using the matrix similarity relation
Since the final objective of the present invention is to obtain the phase delay amount, and the mueller matrix includes the parts related to the depolarization and double attenuation effects, matrix decomposition is performed to remove the parts related to the depolarization and double attenuation effects.
The Lu-Chipman method is carried out on the Mueller matrix M of 4 × 4 to decompose the Mueller matrix M into the following form:
M＝MΔMRMD (13)
wherein M isΔFor a depolarization matrix, MRIs a birefringent matrix, MDFor double attenuation matrices, taking only M of themR。
Will measure the matrix M (z)refAnd z) carrying out matrix decomposition, and eliminating depolarization and double attenuation effects to obtain the Mueller matrix only containing double refraction:
Figure BDA00022717947600000411
wherein M isR(zref,z),
Figure BDA0002271794760000051
And
Figure BDA0002271794760000052
is a Mueller matrix comprising only birefringent components, corresponding to M (z)ref,z),MST(z),MoutAnd Qref。
By utilizing the matrix similarity relation, the phase retardation R under the polar coordinate is calculated by a formula through a measurement Mueller matrix only containing birefringence, and the formula is as follows:
Figure BDA0002271794760000053
tr () represents the trace of the matrix.
6. Converting the phase delay amount from polar coordinates to Cartesian coordinates
And (3) performing coordinate interpolation transformation on the phase retardation under the polar coordinate, converting the polar coordinate into a Cartesian coordinate, and finally obtaining a phase retardation image, namely a polarization image, of the sample of the catheter polarization sensitive optical coherence tomography system.
The coordinate interpolation transformation is that in the data acquisition process of the PS-OCT system, the depth information A-Scan and the transverse information B-Scan are imaged, the final imaging result is a polar coordinate image, but the actual requirement is an image in a lumen, so that the processed polar coordinate image needs to be processed into a PS-OCT image in Cartesian coordinates.
As shown in fig. 3 to 5, which are diagrams illustrating the effect of the polarization demodulation average denoising method for polarization-sensitive optical coherence tomography of a catheter used in the present invention, the left side is an intensity image, the middle is a polarization image under the conventional mueller matrix algorithm, and the right side is a polarization image under the average mueller matrix algorithm. The first line is a chicken breast image processing result, the second line is a pig myocardium image processing result, and the third line is a nail image processing result.
The invention enables the PS-OCT system to completely express the birefringence information of the sample, improves the analysis capability of microscopic lesions in the blood vessel, obtains more characteristic information of atherosclerotic plaques compared with the traditional OCT intensity image, obtains additional analysis capability of the microscopic lesions in the blood vessel by extracting and reading tissue polarization information, and simultaneously enables the birefringence image to have higher definition by reducing noise on average. The method utilizes the polarization characteristics of the Mueller matrix characterization system and the sample, and eliminates the depolarization and double attenuation effects of the system and the sample through matrix decomposition. Noise is weakened through averaging the Mueller matrix, the birefringence phase delay of the sample is obtained through deducing the internal relation between the sample transmission matrix and the PS-OCT signal matrix, namely the condition that the two matrixes are similar and the traces of the similar matrixes are equal, and polarization demodulation of the PS-OCT image of the catheter is realized.
While the present invention has been described with reference to the accompanying drawings, the present invention is not limited to the above-described embodiments, which are illustrative only and not restrictive, and various modifications which do not depart from the spirit of the present invention and which are intended to be covered by the claims of the present invention may be made by those skilled in the art.

Claims (1)

1. A catheter polarization sensitive optical coherence tomography optimized average polarization demodulation method comprises the following steps:
(1) adjusting all three-ring polarization controllers in the system respectively to balance the polarization of the reference light and the input light on two channels of a balance detector H, V;
(2) sample mueller matrix acquisition, denoted by s (z), was as follows:
scanning a sample, obtaining signals H, V by carrying sample information directly acquired by two balanced detectors through numerical dispersion compensation and interpolation Fourier transform, obtaining a segmentation threshold value through autocorrelation peak searching, and segmenting the signals into four parts H1，H2，V1，V2(ii) a Sampling four partial value groups corresponding to the same Z position point of the sample to form a Jones matrix of a pixel point complex signal
Figure FDA0003644496360000011
Converting the image into a Mueller matrix S (z) by using Jones matrix conversion Mueller matrix formula;
(3) and carrying out average processing on the obtained Mueller matrix, wherein the method comprises the following steps:
the mueller matrix at the z position is expressed as:
Figure FDA0003644496360000012
averaging with surrounding points using an averaging window, the averaged mueller matrix is represented as:
Figure FDA0003644496360000013
wherein
Figure FDA0003644496360000014
I is an area contained by the selected average window, t refers to all points in the area, N is the number of points contained by the window, s is a central point of the average window, the averaging process is that the average value in the window replaces a value at the central position, all data points are processed by moving the average window to obtain a Mueller matrix after all the data points are averaged, and the Mueller matrix replaces the original Mueller matrix for calculation;
(4) selecting a special point of a sample as a reference point, and calculating a measurement matrix by using the averaged Mueller matrix, wherein the method comprises the following steps:
determining the outer surface of the catheter or the surface of the sample as reference points, and taking the average of the reference points to write a Mueller matrix
Figure FDA0003644496360000015
Will be provided with
Figure FDA0003644496360000016
And
Figure FDA0003644496360000017
calculating to obtain a measurement matrix M (z) of the sample at zref,z)：
Figure FDA0003644496360000018
MSTIs a sample Mohler matrix, MoutMueller matrix, Q, representing the output beam path of the systemrefAn equivalent Mueller matrix representing the reference light;
(5) performing Mueller matrix decomposition on the measurement matrix, and solving the phase delay amount by utilizing the matrix similarity relation, wherein the method comprises the following steps:
will measure the matrix M (z)refAnd z) carrying out Lu-Chipman matrix decomposition, eliminating depolarization and double attenuation effects to obtain a Mueller matrix only containing double refraction:
Figure FDA0003644496360000021
wherein M isR(zref,z),
Figure FDA0003644496360000022
And
Figure FDA0003644496360000023
is a Mueller matrix comprising only birefringent components, corresponding to M (z)ref,z),MST(z),MoutAnd Qref；
By utilizing the matrix similarity relation, the phase retardation R under the polar coordinate is calculated by using a measurement Mueller matrix only containing birefringence, and the formula is as follows:
Figure FDA0003644496360000024
tr () represents the trace of the matrix;
(6) and (3) performing coordinate interpolation transformation on the phase retardation under the polar coordinate, and converting the polar coordinate into a Cartesian coordinate to obtain a phase retardation image, namely a polarization image, of the sample of the catheter polarization-sensitive optical coherence tomography system.
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