CN209863787U - Holographic endoscopic optical coherence tomography device - Google Patents
Holographic endoscopic optical coherence tomography device Download PDFInfo
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- CN209863787U CN209863787U CN201821899662.7U CN201821899662U CN209863787U CN 209863787 U CN209863787 U CN 209863787U CN 201821899662 U CN201821899662 U CN 201821899662U CN 209863787 U CN209863787 U CN 209863787U
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Abstract
The utility model discloses an optical coherent tomography device is peeped in to holography includes the light source, the broadband light that the light source sent enters into the monochromator, the sweep frequency white light that the output of monochromator sent enters into beam splitter prism, beam splitter prism divide into reference beam, sample beam with the sweep frequency white light, the reference beam shines on the plane mirror, the sample beam shines in the sample tissue through flexible fiber bundle, and the reverberation of reference beam, the scattered light of sample beam assemble formation interference light in beam splitter prism. The utility model can firstly improve the resolution of the OCT system by one order of magnitude and observe a finer biological tissue structure; and secondly, the OCT system can realize three-dimensional real-time imaging, can observe the function change of biological tissues with flow information in real time and evaluate the development of diseases. Finally, all depth resolutions of OCT three-dimensional imaging are kept consistent, which is beneficial to OCT to provide accurate quantitative information of biological tissues.
Description
Technical Field
The utility model belongs to the field, concretely relates to optical coherent tomography device is peeped in to holography.
Background
The lung cancer, liver cancer, stomach cancer and other lesions with the prostate cancer mortality rate are frequently found in internal organs of a human body, and are often located below the surface layer of tissues in the early stage, so that the lesion tissues below the surface layer cannot be found by a conventional electronic endoscope, and an imaging means with a tomography capability is required. Optical Coherence Tomography (OCT) is an emerging technology that has emerged in recent decades and is based on the principle of optical interference, using broadband light sources to achieve high resolution deep tomography with resolution of several microns. The detection and imaging of the internal organs in the human body can be completed by combining the endoscopic probe technology. Endoscopic OCT is expected to be used for early nondestructive rapid detection of diseases such as cancer and the like due to the capabilities of nondestructive, high resolution (-10 um) and three-dimensional imaging and real-time detection.
At present, probes of an endoscopic system are in a scanning mode, mechanical scanning distortion cannot be avoided in scanning, and the imaging speed is limited by a scanning device. In addition, the annular scanning probe is only suitable for tubular regular human body cavities such as blood vessels, esophagus and other tissues. However, most organ cavities of the human body are irregular, and the circular scanning is not suitable. Moreover, the existing endoscopic OCT system uses an infrared light source, and the system resolution is about 10 um. For early diagnosis of cancer and other diseases, a light source with wider bandwidth, such as white light, is required to achieve resolution of submicron level. Therefore, the forward, ultrahigh resolution and parallel imaging endoscopic OCT system has practical significance and is a key for wide application of OCT technology in clinical endoscopy.
Disclosure of Invention
The utility model is provided for solving the problems existing in the prior art, and aims to provide a holographic endoscopic optical coherence tomography device and an imaging method.
The technical scheme of the utility model is that: a holographic endoscopic optical coherence tomography device comprises a light source, wherein broadband light emitted by the light source enters a monochromator, swept white light emitted by an output end of the monochromator enters a beam splitter prism, the beam splitter prism divides the swept white light into a reference beam and a sample beam, the reference beam irradiates a plane mirror, the sample beam irradiates a sample tissue through a flexible optical fiber beam, reflected light of the reference beam and scattered light of the sample beam are converged in the beam splitter prism to form interference light, and the interference light enters an area array detector.
The area array detector is connected with a computing terminal circuit for computing imaging.
The reference light beam is reflected light entering the light splitting prism from the sweep white light, and the sample light beam is refracted light entering the light splitting prism from the sweep white light.
And the refraction output end of the beam splitter prism is provided with a light cone, and the reference beam enters the flexible optical fiber bundle through the light cone.
And the output end of the flexible optical fiber bundle is provided with a self-focusing lens.
The area array detector converts interference light into an interference electric signal.
And the computing terminal receives the interference electric signal, performs zero filling Fourier transform on the interference electric signal, and performs holographic restoration processing to obtain a three-dimensional image of the sample.
The utility model discloses at first can improve an order of magnitude with OCT system resolution ratio, reach 1 micron rank, can observe more tiny biological tissue structure like this. And the OCT system can realize three-dimensional real-time imaging, so that the function change of biological tissues with flow information can be observed in real time, and the development of diseases can be evaluated. Finally, all depth resolutions of OCT three-dimensional imaging are kept consistent, which is beneficial to OCT to provide accurate quantitative information of biological tissues.
Drawings
FIG. 1 is a schematic view of the connection of an image forming apparatus according to the present invention;
FIG. 2 is a method flow diagram of an imaging method of the present invention;
wherein:
1 light source 2 monochromator
3-beam splitter prism 4-plane reflector
5 light cone 6 flexible optical fiber bundle
7 self-focusing lens 8 area array detector
9 calculating the terminal.
Detailed Description
The present invention will be described in detail below with reference to the accompanying drawings and examples:
as shown in fig. 1-2, a holographic endoscopic optical coherence tomography apparatus includes a light source 1, where broadband light emitted by the light source 1 enters a monochromator 2, swept white light emitted by an output end of the monochromator 2 enters a beam splitter prism 3, the beam splitter prism 3 splits the swept white light into a reference beam and a sample beam, the reference beam irradiates a plane mirror 4, the sample beam irradiates a sample tissue through a flexible fiber bundle 6, reflected light of the reference beam and scattered light of the sample beam are converged in the beam splitter prism 3 to form interference light, and the interference light enters an area array detector 8.
The area array detector 8 is connected with a computing terminal 9 circuit for computing imaging.
The reference light beam is reflected light entering the light splitting prism 3 by the sweep white light, and the sample light beam is refracted light entering the light splitting prism 3 by the sweep white light.
The refraction output end of the beam splitter prism 3 is provided with a light cone 5, and the reference beam enters the flexible optical fiber bundle 6 through the light cone 5.
The output end of the flexible optical fiber bundle 6 is provided with a self-focusing lens 7.
The area array detector 8 converts the interference light into an interference electric signal.
And the computing terminal 9 receives the interference electric signal, performs zero filling Fourier transform on the interference electric signal, and performs holographic restoration processing to obtain a three-dimensional image of the sample.
An imaging method of a holographic endoscopic optical coherence tomography device comprises the following steps:
turning on the light source to let visible light into the monochromator
Starting a light source 1, wherein the light source 1 emits broadband light containing a visible band of 400nm-700nm, and the broadband light enters a receiving end of a monochromator 2;
II, triggering and starting the monochromator, setting the working frequency of the monochromator and synchronizing the working frequency to the area array detector
The computing terminal 9 triggers and starts the monochromator 2, the monochromator 2 outputs swept white light according to LHz working frequency, namely the monochromator 2 works L times per second and outputs a series of swept white light each time, and meanwhile the control card of the computing terminal 9 outputs LHz swept synchronous electrical signals to the area array detector 8;
iii, converting broadband light into sweep frequency white light output by monochromator
The monochromator 2 converts the broadband white light into swept-frequency white light and outputs the swept-frequency white light, the output frequency is LHz, the number of the swept-frequency light output each time is K, namely K lights with different wavelengths are output, wherein L is set to be 15Hz, and K is 1000.
Iv, the beam splitter prism divides the sweep white light into a reference beam and a sample beam, and the sample beam enters the sample tissue
The sweep frequency white light enters the beam splitter prism 3 and then is divided into a reference beam and a sample beam, and the sample beam enters a sample tissue;
v. forming interference light by the reflected light of the reference beam and the scattered light of the sample beam and converting the interference light into an interference electric signal
Reflected light of the reference beam and scattered light of the sample beam return to the beam splitter prism 3 to form interference light, wherein the scattered light of the sample beam is light which propagates in the tissue and is back-scattered, and the interference light contains sample tissue information; the area array detector 8 converts the interference light signal after each synchronization moment into an electric signal under the control of a synchronous electric signal of the computing terminal 9, wherein the electric signal is converted for L times per second, and each time comprises K M × N pixel data pictures; wherein M is 300 and N is 400.
Vi, carrying out Fourier transform after zero padding of the interference electric signal, and carrying out holographic image restoration processing, thereby obtaining a three-dimensional structure diagram of the sample
After zero filling, Fourier transformation is carried out on the interference electric signal, and holographic image restoration processing is carried out, so that a three-dimensional structure chart of the sample is obtained, wherein the mark of the interference electric signal is Ij(m,n)，
Where j is 1,2,3 … K, M is 1,2,3 … M, and N is 1,2,3 … N.
And vi, during Fourier transform, performing one-dimensional Fourier transform after supplementing X, K zero values to the K interference signals on each pixel, and taking the first half of data after the transform, and marking as Dj(m,n)，
Where j is 1,2,3 … (X +1) × k/2, where j represents the depth plane, DjAnd (m, n) is sample information of the mth row and the nth column on the jth depth plane, and then holographic image restoration processing is carried out, so that a three-dimensional structure diagram of the sample is obtained.
And vi, the holographic recovery processing process comprises: for each depth plane data Dj(M, N) after two-dimensional Fourier transform, A is obtainedj(M, N) multiplying the mth row and nth column data multiplier data for each plane byNamely, it isWherein i represents an imaginary number, k(m,n)Is the spatial frequency of light, z, corresponding to the pixel positionjIs the specific depth value corresponding to the jth depth plane. k is a radical of(m,n)zjThe product is the phase value, pair DjThe imaginary part and the real and imaginary parts of (m, n) are arctangent calculated to obtain bit phase values, i.e. bit phase valuesThen toCarrying out two-dimensional inverse Fourier transform to obtain three-dimensional data R of holographic restorationj(m,n),Get RjThe (m, n) model gives the three-dimensional structure of the final sample.
The resolution of the OCT image in the depth direction is related to the wavelength and the bandwidth, and the resolution Therefore, if the resolution r in the depth direction needs to be improved, a short wavelength light source is needed and the bandwidth of the light source is increased, the utility model discloses a method for improving the resolution of the liquid crystal display panel, which adopts visible light, the central wavelength is 500nm, the bandwidth is 300nm,compared with the traditional near infrared light 850nm wavelength 100nm bandwidth, the wavelength is short and wide, so that the resolution can be improved to 1 micron order through formula calculation.
No matter be the single-point progressive scan during OCT formation of image or the utility model discloses a parallel imaging, the light source all can disperse when organizing the different degree of depth to propagate, therefore the image data that the detector gathered contain the image information of adjacent formation of image position, especially assembles the plane distance at the out-of-focus plane with the light source, and single image pixel will gather more adjacent data and cause different degree of depth plane resolution inconsistent. This phenomenon is similar to the diffraction propagation of light, and therefore can carry out the counterpropagation according to holographic scalar angle spectrum theory and correct, the utility model discloses a holographic processing procedure is exactly to combine the principle of holographic theory method and OCT to go on.
The utility model discloses at first can improve an order of magnitude with OCT system resolution ratio, reach 1 micron rank, can observe more tiny biological tissue structure like this. And the OCT system can realize three-dimensional real-time imaging, so that the function change of biological tissues with flow information can be observed in real time, and the development of diseases can be evaluated. Finally, all depth resolutions of OCT three-dimensional imaging are kept consistent, which is beneficial to OCT to provide accurate quantitative information of biological tissues.
Claims (7)
1. Holographic endoscopic optical coherence tomography apparatus comprising a light source (1), characterized in that: broadband light emitted by the light source (1) enters the monochromator (2), sweep white light emitted by the output end of the monochromator (2) enters the light splitting prism (3), the sweep white light is split into a reference beam and a sample beam by the light splitting prism (3), the reference beam irradiates the plane reflector (4), the sample beam irradiates sample tissues through the flexible optical fiber beam (6), reflected light of the reference beam and scattered light of the sample beam are converged in the light splitting prism (3) to form interference light, and the interference light enters the area array detector (8).
2. The holographic endoscopic optical coherence tomography apparatus of claim 1, wherein: the area array detector (8) is connected with a computing terminal (9) circuit for computing imaging.
3. The holographic endoscopic optical coherence tomography apparatus of claim 2, wherein: the reference light beam is reflected light entering the light splitting prism (3) by the sweep white light, and the sample light beam is refracted light entering the light splitting prism (3) by the sweep white light.
4. The holographic endoscopic optical coherence tomography apparatus of claim 3, wherein: the refraction output end of the beam splitter prism (3) is provided with a light cone (5), and the reference beam enters the flexible optical fiber bundle (6) through the light cone (5).
5. The holographic endoscopic optical coherence tomography apparatus according to claim 4, wherein: and the output end of the flexible optical fiber bundle (6) is provided with a self-focusing lens (7).
6. The holographic endoscopic optical coherence tomography apparatus of claim 5, wherein: the area array detector (8) converts the interference light into an interference electric signal.
7. The holographic endoscopic optical coherence tomography apparatus of claim 6, wherein: and the computing terminal (9) receives the interference electric signal, performs zero filling Fourier transform on the interference electric signal, and performs holographic restoration processing to obtain a three-dimensional image of the sample.
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111829954A (en) * | 2020-09-09 | 2020-10-27 | 广东工业大学 | System and method for improving full-field sweep optical coherence tomography measuring range |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111829954A (en) * | 2020-09-09 | 2020-10-27 | 广东工业大学 | System and method for improving full-field sweep optical coherence tomography measuring range |
| CN111829954B (en) * | 2020-09-09 | 2023-07-25 | 广东工业大学 | System and method for improving full-field sweep-frequency optical coherence tomography measurement range |
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