CN109164048B - Polarization demodulation method for polarization-sensitive optical coherence tomography of catheter - Google Patents
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Abstract
A method of polarization demodulation for catheter polarization-sensitive optical coherence tomography, comprising: setting the polarization state of input light of a catheter polarization-sensitive optical coherence tomography system; setting the reference light on the H and V paths in the system as the isocandela; performing dispersion compensation, interpolation Fourier transform and image segmentation on the electric signals measured at the polarization diversity; converting the Jones matrix at the sample depth and the reference surface position into a Mueller matrix; multiplying the Mueller matrix at the sample depth by the inverse matrix of the Mueller matrix at the reference surface position to obtain a measured Mueller matrix of the sample; eliminating depolarization and double attenuation effects; measuring the Mueller matrix to obtain a phase delay amount under a polar coordinate; and converting the phase retardation under the polar coordinate into a Cartesian coordinate from the polar coordinate, and finally obtaining a birefringent image of the sample of the catheter polarization sensitive optical coherence tomography system. The invention can solve the problem that the guide tube cannot demodulate the birefringence information of the sample in a high-speed rotating state.
Description
Technical Field
The invention relates to a catheter optical coherence tomography method. In particular to a polarization demodulation method for catheter polarization sensitive optical coherence tomography.
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 system has reached a level that may determine the property of the tissue plaque in terms of resolution, but is still insufficient in terms of tissue penetration ability, image sharpness, and accuracy of tissue plaque type determination, and using the PS-OCT technology, improving the performance of the related technology is a key direction for development of the OCT system, and is also a necessary way to solve the aforementioned key scientific problems.
In catheter OCT, catheter PS-OCT is an extension of catheter OCT technology, which provides a quantitative measure of tissue birefringence properties. The birefringence of light changes the polarization state of light and can be associated with proteins and biological macromolecules with oriented structures such as collagen, actin, and the like. The enhanced birefringence phenomenon of catheter PS-OCT is closely related to the existence of a large amount of thick collagen fibers or intimal smooth muscle cells, so that the high-resolution detection of catheter PS-OCT imaging can be applied to the enhanced plaque stability measurement. In addition, catheter PS-OCT systems have the potential to assess plaque collagen and differentiate normal intima, fibrous plaque, lipid plaque, and calcified plaque, among others. The existing polarization demodulation method utilizes a Jones matrix to characterize the polarization characteristics of a system and a sample. However, in catheter PS-OCT, the fiber inside the catheter needs to be rotated at high speed, so that there are strong depolarization and double attenuation effects in the system.
Disclosure of Invention
The technical problem to be solved by the invention is to provide a polarization demodulation method capable of realizing polarization demodulation of a PS-OCT image of a catheter.
The technical scheme adopted by the invention is as follows: a polarization demodulation method for catheter polarization-sensitive optical coherence tomography is used for a catheter polarization-sensitive optical coherence tomography system and comprises the following steps:
1) setting the polarization state of input light of a catheter polarization-sensitive optical coherence tomography system to Ein(ii) a Setting the reference light on the H and V paths in the system as the isocandela; performing dispersion compensation and interpolation Fourier transform on the electric signals measured at the polarization diversity position, and then performing image segmentation; respectively converting the Jones matrix at the sample depth position and the selected reference surface position into a Mueller matrix; multiplying the Mueller matrix at the sample depth position by the inverse matrix of the Mueller matrix at the selected reference surface position to obtain a measured Mueller matrix of the sample;
2) eliminating depolarization and double attenuation effects through matrix decomposition;
3) the Mueller matrix M (z) will be measuredrefZ) obtaining a phase delay amount R in polar coordinates through calculation;
4) 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 birefringent image of the sample of the catheter polarization-sensitive optical coherence tomography system.
Polarization state E described in step 1)inExpressed as:
wherein Hin1Is the input polarization state-the light intensity in the H channel, Hin2Is the light intensity, V, of the input polarization state two in the H channelin1Is the input polarization state-the light intensity in the V channel, Vin2Is the light intensity of the input polarized light two in the V channel, wherein the input polarized states one and two are isocandela in the H path and the V path,
is the phase difference of the two polarization states of the input light on the H and V paths.
The reference light set to the isocandela intensity on the H and V paths in the system described in step 1) is expressed as:
wherein HrefAnd VrefAre the orthogonal components of the reference light on the H-channel and V-channel, respectively, and ψ is the phase difference of the polarization state of the reference light on the H-and V-channels.
The conversion method for respectively converting the Jones matrix at the sample depth position and the selected reference surface position into the Mueller matrix in the step 1) comprises the following steps:
the jones matrix is represented as:
wherein a, b, c, d are any four elements of the Jones matrix,
the conversion relation between the Jones matrix and the Mueller matrix is as follows:
wherein
Representing the Kronecker product, U represents the transformation matrix:
according to the conversion relation between the Jones matrix and the Mueller matrix, the Jones matrix Q (z) at the position of the sample depth and the Jones matrix Q (z) at the position of the selected reference surface are obtainedref) Respectively converted into Mueller matrices
Let MSTIs a sample round-trip matrix, Min，MoutMueller matrix representing the optical path of the system, Mueller matrix S (z) at the position of the reference plane of the sample measured at polarization diversityref) Expressed as:
mueller matrix s (z) at sample z position measured at polarization diversity, expressed as:
mixing S (z)ref) And S (z) operating to obtain a measurement matrix M (z) of the sample at zref,z)：
Eliminating depolarization and double attenuation effects through matrix decomposition in the step 2), comprising:
the mueller matrix M of 4 x 4 is decomposed:
M＝MΔMRMD (11)
wherein M isΔFor a depolarization matrix, MRIs a birefringent matrix, MDFor a double-attenuation matrix, the final purpose of the method is to eliminate the depolarization and double-attenuation effects in the Mueller matrix, and further obtain a double-refraction matrix MR。
Will measure the matrix M (z)refAnd z) carrying out matrix decomposition, and eliminating depolarization and double attenuation effects to obtain a Mueller matrix only containing double refraction:
wherein M isR(zref,z),
And
is a Mueller matrix comprising only birefringent components, in which case
Is a unitary matrix, MR(zrefZ) and
is a similarity matrix.
The phase delay R under the polar coordinate in the step 3) is obtained by the following formula:
in the formula (I), the compound is shown in the specification,
a mueller matrix is detected at the z position of the sample, which contains only birefringent components, and tr is the trace of the matrix.
The invention discloses a Polarization demodulation method for catheter Polarization-sensitive optical coherence tomography, and relates to a method for demodulating birefringence information of a sample in a catheter Polarization-sensitive optical coherence tomography (Polarization-sensitive OCT) image, namely a PS-OCT image, and the problem that the catheter cannot demodulate the birefringence information of the sample in a high-speed rotating state can be solved. The invention enables the PS-OCT system to completely express the birefringence information of the sample, improves the analysis capability of microscopic lesions in blood vessels, obtains more characteristic information of atherosclerotic plaques compared with the traditional OCT intensity image, and obtains additional analysis capability of microscopic lesions in blood vessels by extracting and reading the tissue polarization information. 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. The sample birefringence phase delay is obtained by 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, so that the polarization demodulation of the PS-OCT image of the catheter is realized.
Drawings
FIG. 1 is a schematic diagram of a catheter polarization-sensitive optical coherence tomography system of the present invention;
FIG. 2 is a flow chart of a method for polarization demodulation for catheter polarization sensitive optical coherence tomography of the present invention.
Detailed Description
The following describes a polarization demodulation method for catheter polarization-sensitive optical coherence tomography according to the present invention in detail with reference to the following embodiments and the accompanying drawings.
The polarization demodulation 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 sample birefringence phase delay is obtained by 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, so that the polarization demodulation of the PS-OCT image of the catheter is realized.
The invention discloses a polarization demodulation method for catheter polarization-sensitive optical coherence tomography, which is characterized in that a series of calculations and transformations are carried out on time domain data acquired by a balanced detector, the relation between a catheter PS-OCT signal matrix and a sample Jones matrix is deduced, the interference of an external environment and a transmission matrix of an optical fiber light path on the phase delay of the sample is eliminated, and then the PS-OCT image polarization demodulation method on a catheter is provided through the transformation from the Jones matrix to a Mueller matrix and the decomposition of Mueller. In the catheter PS-OCT system, the birefringence information of the sample can be correctly demodulated under the state that the catheter rotates at high speed.
The invention relates to a polarization demodulation method for catheter polarization-sensitive optical coherence tomography, 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 first port 21 of a 1:99 optical fiber coupler 2 and is distributed to a sample arm and a reference arm from a second port 22 and a third port 23 of the first optical fiber coupler 2 in a ratio of 1: 99. Emergent light of a second port 22 of a first optical fiber coupler 2 of 1:99 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 first three-ring polarization controller 3, enter a first port 24 of a first circulator 6, light exits from a second port 25 of the first circulator 6, the emergent light enters an imaging guide pipe 11 through a rotating mechanism 8, and the light reflected by the sample returns to the first circulator 6 from the imaging guide pipe 11 and exits through a third port 26 of the first circulator 6. Emergent light of the third port 23 of the 1:99 optical fiber coupler 2 enters the reference arm, the light entering the reference arm enters the single-mode optical fiber 5 with the length of 18.5 meters, the emergent light enters the first port 27 of the second circulator 7, exits from the second port 28 of the second circulator 7 and enters the reflective optical fiber delay line 10, and the reflected light enters through the second port 28 of the second circulator 7 and exits from the third port 29 to the second triple-ring polarization controller 9. The emergent light of the sample arm passing through the third port 26 of the circulator 6 and the emergent light of the reference arm passing through the third ring polarization controller 9 are respectively incident into the third ring polarization controller 13 and the fourth ring polarization controller 14 from the first port 30 and the second port 31 of the second fiber coupler 12 in a ratio of 50:50, the emergent light enters into the third ring polarization controller 13 and the fourth ring polarization controller 14 from the third port 32 and the fourth port 33 respectively in a ratio of 50:50, the emergent light enters into the first polarization beam splitter 15 and the second polarization beam splitter 16 respectively, the emergent light of the first polarization beam splitter 15 enters into the balance detectors 17 and 18 from the first port 34 and the second port 35 of the first polarization beam splitter 15 respectively, the emergent light of the second polarization beam splitter 16 enters into the first balance detector 17 and the second balance detector 18 from the first port 36 and the second port 37 of the second polarization beam splitter 16 respectively, the electrical signals of the first and second balanced detectors 17, 18 are received by the acquisition card 19 and transmitted to the 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 method for catheter polarization-sensitive optical coherence tomography of the present invention comprises the following steps:
1) setting a polarization state of input light of a catheter polarization-sensitive optical coherence tomography (PS-OCT) system to Ein(ii) a Setting reference light on an H path and a V path in the system as equal light intensity; performing dispersion compensation and interpolation Fourier transform on the electric signals measured at the polarization diversity position, and then performing image segmentation; respectively converting the Jones matrix at the position of the detected sample depth and the position of the selected reference surface into a Mueller matrix; multiplying the Mueller matrix at the sample depth position by the inverse matrix of the Mueller matrix at the selected reference surface position to obtain a measurement matrix of the sample; wherein the content of the first and second substances,
(1) said polarization state EinExpressed as:
wherein Hin1Is the input polarization state-the light intensity in the H channel, Hin2Is the light intensity, V, of the input polarization state two in the H channelin1Is the input polarization state-the light intensity in the V channel, Vin2Is the light intensity of the input polarized light two in the V channel, wherein the input polarized states one and two are isocandela in the H path and the V path,
is the phase difference of the two polarization states of the input light on the H and V paths.
(2) The reference light set to the isocandela intensity on the H and V paths in the system is expressed as:
wherein HrefAnd VrefAre the orthogonal components of the reference light on the H-channel and V-channel, respectively, and ψ is the phase difference of the polarization state of the reference light on the H-and V-channels.
(3) The conversion method for respectively converting the Jones matrix at the detected sample depth position and the selected reference surface position into the Mueller matrix comprises the following steps:
the jones matrix is represented as:
wherein a, b, c, d are any four elements of the Jones matrix,
the conversion relation between the Jones matrix and the Mueller matrix is as follows:
wherein
Representing the Kronecker product, U represents the transformation matrix:
according to the conversion relation between the Jones matrix and the Mueller matrix, the Jones matrix Q (z) at the position of the detected sample depth and the Jones matrix Q (z) at the position of the selected reference surface are obtainedref) Respectively converted into Mueller matrices
H and V channels measured at polarization diversityThe two-channel signal H is obtained by respectively carrying out dispersion compensation and interpolation Fourier transform on the directly acquired electric signal1+H2，V1+V2H is obtained by image segmentation1，H2，V1，V2The four images of (2). Taking an A-line as an example, a Jones matrix J (z) ═ H of pixel point complex signals at a z position of the depth of a sample is constructed1(z) H2(z)；V1(z) V2(z)]And a reference plane zrefJones matrix J (z) of position pixel point complex signalref)＝[H1(zref) H2(zref)；V1(zref) V2(zref)]The reference surface can be selected from the outer surface of the catheter or the surface of the sample, and is converted into S (z) and S (z) of the Mueller matrix by using the formulas (4) and (5)ref)。
Let MSTIs a sample round-trip matrix, Min，MoutMueller matrix representing the optical path of the system, Mueller matrix S (z) at the position of the reference plane of the sample measured at polarization diversityref) Expressed as:
mueller matrix s (z) at sample z position measured at polarization diversity, expressed as:
mixing S (z)ref) And S (z) operating to obtain a measurement matrix M (z) of the sample at zref,z)：
2) To construct M (z)refZ) and MS,T(z) is a similarity matrix, requiring QZrefMoutIs unitary matrix, but if QZrefMoutInvolving depolarization and doubletAttenuation effects, the condition of the similarity matrix does not hold. QZrefIs a unitary matrix, but in a catheter PS-OCT system, the high-speed rotation of the optical fiber in the catheter necessarily brings strong depolarization and double attenuation effects, so MoutThe method comprises the depolarization and double attenuation effects, and the depolarization and double attenuation effects need to be eliminated through matrix decomposition. Eliminating the depolarization and double attenuation effects by matrix decomposition includes:
the mueller matrix M of 4 x 4 is decomposed:
M＝MΔMRMD (11)
wherein M isΔFor a depolarization matrix, MRIs a birefringent matrix, MDFor a double-attenuation matrix, the final purpose of the method is to eliminate the depolarization and double-attenuation effects in the Mueller matrix, and further obtain a double-refraction matrix MR。
Will measure the matrix M (z)refAnd z) carrying out matrix decomposition, and eliminating depolarization and double attenuation effects to obtain a Mueller matrix only containing double refraction:
wherein M isR(zref,z),
And
is a Mueller matrix comprising only birefringent components, in which case
Is a unitary matrix, MR(zrefZ) and
is a similarity matrix.
3) Will measure the matrix M (z)refZ) obtaining a phase delay amount R in polar coordinates through calculation; the phase delay R in polar coordinates is obtained by the following formula：
In the formula (I), the compound is shown in the specification,
a mueller matrix is detected at the z position of the sample, which contains only birefringent components, and tr is the trace of the matrix.
4) 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 birefringent 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 a Cartesian coordinate.
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 (6)
1. A polarization demodulation method for catheter polarization-sensitive optical coherence tomography is used for a catheter polarization-sensitive optical coherence tomography system and is characterized by comprising the following steps:
1) setting the polarization state of input light of a catheter polarization-sensitive optical coherence tomography system to Ein(ii) a Setting the reference light on the H and V paths in the system as the isocandela; performing dispersion compensation and interpolation Fourier transform on the electric signals measured at the polarization diversity position, and then performing image segmentation; the sample depth position and the selected reference surface position are combinedConverting the Jones matrix into a Mueller matrix; multiplying the Mueller matrix at the sample depth position by the inverse matrix of the Mueller matrix at the selected reference surface position to obtain a measured Mueller matrix of the sample;
2) eliminating depolarization and double attenuation effects through matrix decomposition;
3) the Mueller matrix M (z) will be measuredrefZ) obtaining a phase delay amount R in polar coordinates through calculation;
4) 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 birefringent image of the sample of the catheter polarization-sensitive optical coherence tomography system.
2. The polarization demodulation method for catheter polarization-sensitive optical coherence tomography according to claim 1, wherein the polarization state E in step 1)inExpressed as:
wherein Hin1Is the input polarization state-the light intensity in the H channel, Hin2Is the light intensity, V, of the input polarization state two in the H channelin1Is the input polarization state-the light intensity in the V channel, Vin2Is the light intensity of the input polarized light two in the V channel, wherein the input polarized states one and two are isocandela in the H path and the V path,
is the phase difference of the two polarization states of the input light on the H and V paths.
3. The polarization demodulation method for catheter polarization-sensitive optical coherence tomography according to claim 1, wherein the reference light set to equal intensity in the H and V paths in the system of step 1) is represented as:
wherein HrefAnd VrefAre the orthogonal components of the reference light on the H-channel and V-channel, respectively, and ψ is the phase difference of the polarization state of the reference light on the H-and V-channels.
4. The polarization demodulation method for polarization-sensitive optical coherence tomography of catheter according to claim 1, wherein the conversion method for converting the jones matrix at the sample depth position and the selected reference plane position into the mueller matrix in step 1) comprises:
the jones matrix is represented as:
wherein a, b, c, d are any four elements of the Jones matrix,
the conversion relation between the Jones matrix and the Mueller matrix is as follows:
wherein
Representing the Kronecker product, U represents the transformation matrix:
according to the conversion relation between the Jones matrix and the Mueller matrix, the Jones matrix Q (z) at the position of the sample depth and the Jones matrix Q (z) at the position of the selected reference surface are obtainedref) Respectively converted into Mueller matrices
Let MSTIs a sample round-trip matrix, Min，MoutMueller matrix representing the optical path of the system, Mueller matrix S (z) at the position of the reference plane of the sample measured at polarization diversityref) Expressed as:
mueller matrix s (z) at sample z position measured at polarization diversity, expressed as:
mixing S (z)ref) And S (z) operating to obtain a measurement matrix M (z) of the sample at zref,z)：
5. The polarization demodulation method for catheter polarization-sensitive optical coherence tomography according to claim 1, wherein the elimination of depolarization and double attenuation effects by matrix decomposition in step 2) comprises:
the mueller matrix M of 4 x 4 is decomposed:
M＝MΔMRMD (11)
wherein M isΔFor a depolarization matrix, MRIs a birefringent matrix, MDFor a double-attenuation matrix, the final purpose of the method is to eliminate the depolarization and double-attenuation effects in the Mueller matrix, and further obtain a double-refraction matrix MR；
Will measure the matrix M (z)refAnd z) carrying out matrix decomposition, and eliminating depolarization and double attenuation effects to obtain a Mueller matrix only containing double refraction:
wherein M isR(zref,z),
And
is a Mueller matrix comprising only birefringent components, in which case
Is a unitary matrix, MR(zrefZ) and
is a similarity matrix.
6. The polarization demodulation method for catheter polarization-sensitive optical coherence tomography according to claim 1, wherein the phase retardation R in polar coordinates in step 3) is obtained by the following formula:
in the formula (I), the compound is shown in the specification,
a mueller matrix is detected at the z position of the sample, which contains only birefringent components, and tr is the trace of the matrix.
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| CN110584613A (en) * | 2019-10-09 | 2019-12-20 | 南京沃福曼医疗科技有限公司 | Catheter polarization sensitive optical coherence tomography system and demodulation method |
| CN110749553A (en) * | 2019-10-09 | 2020-02-04 | 南京沃福曼医疗科技有限公司 | Method for improving demodulation effect of catheter polarization sensitive optical coherence tomography |
| CN110742584A (en) * | 2019-10-09 | 2020-02-04 | 南京沃福曼医疗科技有限公司 | Polarization resolving method for catheter polarization sensitive optical coherence tomography demodulation method |
| CN110742582A (en) * | 2019-10-09 | 2020-02-04 | 南京沃福曼医疗科技有限公司 | Binary image segmentation method for catheter polarization-sensitive optical coherence tomography |
| CN110742583A (en) * | 2019-10-09 | 2020-02-04 | 南京沃福曼医疗科技有限公司 | Spectral shaping method for polarization-sensitive optical coherence tomography demodulation of catheter |
| CN110954481B (en) * | 2019-11-13 | 2022-07-01 | 天津大学 | Optimized average polarization demodulation method for catheter polarization sensitive optical coherence tomography |
| CN110731755A (en) * | 2019-12-03 | 2020-01-31 | 南京沃福曼医疗科技有限公司 | Polarization leveling method of catheter polarization-sensitive optical coherence tomography system |
| CN111122452B (en) * | 2019-12-28 | 2022-10-11 | 天津大学 | De-scattering imaging method based on Mueller matrix |
| CN111965114B (en) * | 2020-08-15 | 2023-08-29 | 天津大学 | Catheter polarization sensitive optical coherence tomography local birefringence demodulation method |
| CN112763422A (en) * | 2021-02-02 | 2021-05-07 | 深圳英美达医疗技术有限公司 | Polarization sensitive detection light splitting system and light splitting detection method thereof |
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| CN113888478B (en) * | 2021-09-15 | 2022-11-11 | 天津大学 | Optimized depolarization method for intravascular catheter polarization-sensitive coherent tomography |
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