CN107328743B - Optical coherent confocal microscopy endoscope system and implementation method - Google Patents
Optical coherent confocal microscopy endoscope system and implementation method Download PDFInfo
- Publication number
- CN107328743B CN107328743B CN201710542960.4A CN201710542960A CN107328743B CN 107328743 B CN107328743 B CN 107328743B CN 201710542960 A CN201710542960 A CN 201710542960A CN 107328743 B CN107328743 B CN 107328743B
- Authority
- CN
- China
- Prior art keywords
- optical fiber
- light beam
- light source
- optical
- processing module
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
- G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
Landscapes
- Health & Medical Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- Chemical & Material Sciences (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- General Health & Medical Sciences (AREA)
- General Physics & Mathematics (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
The invention discloses an optical coherence confocal microscopy endoscope system and an implementation method, wherein a section of 4F optical system is added at an OCT scanning imaging end, and the section of optical system is conveniently used in an endoscope cavity channel, so that the aperture of an optical fiber of a sample arm is smaller than the minimum beam diameter (namely the minimum resolution of an objective lens) of an imaging surface, and the system has a confocal imaging effect; therefore, the resolution of OCT can be obviously improved while the imaging depth is not obviously reduced, the imaging effect similar to that of co-focusing is achieved under the condition of no dyeing, and the use of the MEMS micro-vibrating mirror and the calling of GPU/FPGA algorithm are combined and shared with the existing endoscope system in an integrated mode, so that the OCT imaging system becomes a medical diagnosis tool which is rapid, free of dyeing, high in sensitivity and specificity.
Description
Technical Field
The invention relates to a endomicroscopy system, in particular to an optical coherent confocal endomicroscopy system and an implementation method thereof.
Background
In the field of medical diagnosis, since the lesion often occurs on the superficial tissue, medical staff should observe not only microscopic imaging of the surface of biological tissue, but also observe the structure and morphology of the tissue to find micro lesions. For the existing tomography technology, such as ultrasonic imaging, the resolution is low while the imaging depth is deep, and the requirement of finding tiny lesions is not met.
An Optical Coherence Tomography (OCT) is used as an imaging means with high resolution, the principle of the OCT is based on a low coherence interference technology, the advantages of heterodyne detection and conjugate imaging are combined, reflected light signals collected from a sample end are collected, a three-dimensional chromatographic image of the sample is calculated and restored, important information such as the internal structure and scattering coefficient of biological tissues is reflected, the imaging depth is 3-6mm, superficial pathological change tissues are covered, the longitudinal resolution reaches 1-10 microns, and the OCT has the advantages of non-contact, no mark and the like. The application of OCT technology to ophthalmic imaging has become one of the gold standards for ophthalmic diagnosis, and in recent years, there are many reports that OCT technology is applied to tissue mucosa detection of early-stage cervical cancer, skin cancer and cardiovascular lesions, and the OCT technology has great application prospects and development potentials, and it has become a research hotspot that a combination of multiple imaging modes provides more accurate diagnosis bases.
However, in general, the magnification of the OCT system is limited by the scanning lens, the lateral resolution is not high, the longitudinal resolution also decreases with the depth, and it is difficult to balance the imaging depth and the resolution. Under a microscope objective with a high numerical aperture, the lateral resolution of up to 0.1um is realized through the conjugate relationship between an illumination pinhole and a detection pinhole to an irradiated point or a detected point, but the depth of confocal scanning imaging is shallow, and a fluorescent agent is required to dye a sample, detect fluorescence and image, so that the application range of the confocal scanning imaging is limited. Therefore, both OCT techniques and confocal microscopy have advantages and disadvantages.
Patent CN 102818768A proposes a multifunctional biomedical microscope, which combines the OCT and the two sets of co-focusing system structures together, but it is still the simultaneous and independent imaging of the two sets of systems, and does not achieve the effects of simplifying the system structure and operation and improving the system performance.
Therefore, no new imaging technology and endoscope implementation method combining the advantages of the two technologies has been proposed for the time being, and the prior art still needs to be improved and developed.
Disclosure of Invention
The invention aims to provide an optical coherence confocal microscopy endoscope system and an implementation method thereof, and aims to solve the problems that in the prior art, high-lateral-resolution OCT imaging without dyeing cannot be realized through one system, and the system structure and operation cannot be simplified and the system performance effect cannot be improved by directly splicing two sets of system structures of OCT and confocal OCT together.
The technical scheme of the invention is as follows: an optically coherent confocal endomicroscopy system comprising:
the OCT system comprises a host module, a laser module, a scanning module and a control module, wherein the host module takes an OCT structure as a main body and comprises a guide light source, a wavelength division multiplexer, a swept-frequency light source, an optical fiber circulator, an optical fiber coupler and a reference arm;
the probe imaging module takes the confocal structure as a main body, obtains a sample interference signal by scanning a sample and has a confocal imaging effect;
the comprehensive control processing module is used for detecting and acquiring interference signals and processing and operating the acquired interference signals to obtain images;
the optical fiber circulator comprises three ports a, b and c which are arranged clockwise, and a guide light source and a wavelength division multiplexer, a sweep frequency light source and an a port of the optical fiber circulator, the wavelength division multiplexer and an optical fiber coupler, a b port of the optical fiber circulator and the optical fiber coupler, the optical fiber coupler and a reference arm, the optical fiber coupler and a probe imaging module, the wavelength division multiplexer and a comprehensive control processing module, and a c port of the optical fiber circulator and the comprehensive control processing module are respectively connected through single mode fibers; the sweep frequency light source is connected with the comprehensive control processing module, and the sweep frequency light source controls the comprehensive control processing module to acquire interference signals; the comprehensive control processing module is respectively connected with the reference arm and the probe imaging module, and controls the reference arm and the probe imaging module to adjust the scanning and imaging ranges: the guiding light source emits a light source light beam, and the light beam reaches the optical fiber coupler through single-mode optical fiber coupling and transmission of the wavelength division multiplexer; the sweep frequency light source emits a light source light beam which is transmitted to the optical fiber coupler through the port a and the port b of the optical fiber circulator in sequence; two beams of light source beams are divided into a first beam and a second beam after passing through the optical fiber coupler, the first beam forms a reference signal beam after being processed by a reference arm and returns to the optical fiber coupler in the original path, the second beam is processed by the probe imaging module and images a sample to obtain a sample signal beam with a confocal scanning imaging effect, the sample signal beam returns to the optical fiber coupler in the original path, the reference signal beam and the sample signal beam return to the wavelength division multiplexer and a port b and a port c of the optical fiber circulator respectively after being interfered in the optical fiber coupler, finally, an interference signal is detected and collected by the comprehensive control processing module, the comprehensive control processing module processes and operates the interference signal, and a three-dimensional image with a certain depth and a transverse section image with a specific depth are generated rapidly.
The optical coherent confocal microscopy endoscope system is characterized in that the splitting ratio of the optical fiber coupler is 10:90.
the typical central wavelength of the swept-frequency light source is 840nm, 1310nm or 1550nm, and the bandwidth is more than 50nm.
The optical coherence confocal microscopy endoscope system is characterized in that the reference arm comprises an optical fiber polarization controller, a first collimating lens, a focusing lens and an optical delay line, and the optical delay line is connected with the comprehensive control processing module and is controlled by the comprehensive control processing module; the first light beam is modulated by the optical fiber polarization controller to enable the polarization state of the first light beam to be matched with that of the second light beam, then the first light beam sequentially passes through the first collimating lens, the focusing lens and the optical delay line, the optical delay line adjusts the optical path of the first light beam in real time to enable the optical path of the first light beam to be matched with that of the second light beam, and finally a reference signal light beam is formed and returns to the optical fiber coupler in the original path.
The optical coherence confocal microscopy endoscope system comprises a probe imaging module, a scanning lens, a double-cemented lens and a microscope objective, wherein the probe imaging module comprises a second collimating lens, an MEMS micro-vibration lens for controlling the deflection angle of a light beam, the scanning lens and the double-cemented lens are designed to form an optical 4F system structure for modulating the light beam, and the MEMS micro-vibration lens is connected with a comprehensive control processing module and is controlled by the comprehensive control processing module; and the second light beam is emitted through the second collimating lens, sequentially enters the MEMS micro-vibration lens, the scanning lens and the double-cemented lens, finally images the sample through the micro-objective lens to obtain a sample signal light beam with a confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler in the original path.
The optical coherence confocal microscopy endoscope system is characterized in that the focal lengths of the scanning lens and the double-cemented lens need to satisfy the following relation:
Wherein f2 is the focal length of the scanning lens, f3 is the focal length of the double-cemented lens, NA is the numerical aperture of the microscope objective, and d is the fiber diameter of the single-mode fiber.
The optical coherence confocal microscopy endoscope system is characterized in that the probe imaging module comprises a protective sleeve, a cavity, piezoelectric ceramics, a double-cemented lens and a microscope objective, wherein the piezoelectric ceramics are driven by voltage to carry out two-axis adjustment and drive a single-mode optical fiber to vibrate so as to realize light beam scanning; the second light beam sequentially passes through the cavity, the piezoelectric ceramic and the double-cemented lens, and finally images the sample through the microscope objective to obtain a sample signal light beam with a confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler in the original path.
The optical coherence confocal microscopy endoscope system comprises an integrated control processing module and a light ring device, wherein the integrated control processing module comprises a balance detector for detecting interference signals, an acquisition card for acquiring the interference signals detected by the balance detector and a processing module for processing and operating the interference signals acquired by the acquisition card and obtaining images, and the balance detector is respectively connected with a wavelength division multiplexer and a port c of the light ring device through single-mode optical fibers; the acquisition card is connected with the sweep frequency light source, the sweep frequency light source outputs a clock and a trigger signal, and the acquisition card is controlled to acquire an interference signal of a specific period output by the balance detector; the processing module is respectively connected with the probe imaging module and the reference arm, and the processing module respectively controls the probe imaging module and the reference arm, and adjusts the scanning and imaging ranges by combining the positioning of the guide light source.
An implementation method of an optical coherent confocal endomicroscopy system comprises the following steps:
step S100: guiding a light source beam emitted by a light source to reach the optical fiber coupler through single-mode optical fiber coupling and transmission of a wavelength division multiplexer; light source beams emitted by the sweep frequency light source are transmitted to the optical fiber coupler through the port a and the port b of the optical fiber circulator in sequence;
step S200: the two light source light beams are divided into two paths at the optical fiber coupler, and the two paths are respectively a first light beam and a second light beam;
step S300: the first light beam is processed by the reference arm to form a reference signal light beam and returns to the optical fiber coupler in the original path; the second light beam is processed by the probe imaging module and images a sample to obtain a sample signal light beam with a confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler in the original path;
step S400: the reference signal beam and the sample signal beam interfere in the optical fiber coupler, and interference optical signals respectively return to a port b and a port c of the wavelength division multiplexer and the optical fiber circulator;
step S500: interference light signals in the wavelength division multiplexer and the optical fiber circulator are detected by the balance detector, the sweep frequency light source controls the acquisition card to acquire interference signals of a specific period output by the balance detector, and the processing module processes and operates the interference signals acquired by the acquisition card to obtain a three-dimensional image with a certain depth and a transverse section image with a specific depth.
The implementation method of the optical coherence confocal endomicroscopy system comprises the following steps of S500: after acquiring an interference signal of a complete galvanometer cycle from an acquisition card, a processing module realizes FFT (fast Fourier transform algorithm) operation, interpolation zero filling, frequency spectrum filtering and subsequent image optimization processing through GPU (graphic processing Unit) or PFGA (pulse frequency acquisition) hardware, quickly generates a three-dimensional image with a certain depth, and intercepts a transverse sectional view with a specific depth as an image of an OCM (optical coherence tomography); or the processing module directly stores the voltage value in the GPU or the FPGA after acquiring an interference signal of a complete galvanometer cycle from the acquisition card, and directly outputs the calculated transverse section result as an OCM image.
The invention has the beneficial effects that: the invention provides an optical coherence confocal microscopy endoscope system and an implementation method, wherein a section of 4F optical system is added at an OCT scanning imaging end, and the section of optical system is conveniently used in an endoscope cavity channel, so that the aperture of an optical fiber of a sample arm is smaller than the minimum beam diameter (namely the minimum resolution of an objective lens) of an imaging surface, and the system has a confocal imaging effect; therefore, the resolution of OCT can be obviously improved while the imaging depth is not obviously reduced, the imaging effect similar to that of co-focusing is achieved under the condition of no dyeing, and the use of the MEMS micro-vibrating mirror and the calling of GPU/FPGA algorithm are combined and shared with the existing endoscope system in an integrated mode, so that the OCT imaging system becomes a medical diagnosis tool which is rapid, free of dyeing, high in sensitivity and specificity.
Drawings
FIG. 1 is a schematic diagram of the structure of an optical coherent confocal endomicroscopy system according to the present invention.
Fig. 2 is a schematic structural diagram of a second embodiment of the probe imaging module of the invention.
Fig. 3 is a flow chart of steps of a method for implementing the optical coherence confocal endomicroscopy system of the invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention clearer and clearer, the present invention is further described in detail below with reference to the accompanying drawings and examples.
As shown in fig. 1, an Optical coherence confocal microscopy system adds a 4F Optical system at the scanning and imaging end of OCT (Optical coherence tomography), which is conveniently used in the Endoscopic lumen, and is called as OCM endoscope (Endoscopic coherence microscopy), which specifically includes:
the OCT system comprises a host module 19 which takes an OCT structure as a main body, wherein the host module 19 comprises a guide light source 1, a wavelength division multiplexer 3, a sweep light source 2, a fiber circulator 4, a fiber coupler 5 and a reference arm;
a probe imaging module 9 (i.e. a sample arm in the OCT imaging system) which takes a confocal structure as a main body, obtains a sample interference signal by scanning a sample, and has a confocal imaging effect;
a comprehensive control processing module 20 for detecting and collecting interference signals and processing and operating the collected interference signals to obtain images;
the optical fiber circulator 4 comprises ports a, b and c which are arranged clockwise, and a guide light source 1 and a wavelength division multiplexer 3, a sweep light source 2 and the port a of the optical fiber circulator 4, the wavelength division multiplexer 3 and an optical fiber coupler 5, the port b of the optical fiber circulator 4 and the optical fiber coupler 5, the optical fiber coupler 5 and a reference arm, the optical fiber coupler 5 and a probe imaging module 9, the wavelength division multiplexer 3 and a comprehensive control processing module 20, and the port c of the optical fiber circulator 4 and the comprehensive control processing module 20 are respectively connected through single-mode optical fibers; the sweep frequency light source 2 is connected with the comprehensive control processing module 20, and the sweep frequency light source 2 controls the comprehensive control processing module 20 to collect interference signals; the comprehensive control processing module 20 is respectively connected with the reference arm and the probe imaging module 9, and controls the reference arm and the probe imaging module 9 to adjust the scanning and imaging ranges: the light source 1 is guided to emit a beam of laser, and the laser is coupled by a single-mode fiber and transmitted by the wavelength division multiplexer 3 to reach the fiber coupler 5; the sweep frequency light source 2 emits a light source beam, the light source beam sequentially passes through an a port and a b port of the optical fiber circulator 4 and is conducted to the optical fiber coupler 5, the light beam is divided into a first light beam and a second light beam after passing through the optical fiber coupler 5, the first light beam is processed by a reference arm to form a reference signal beam, the reference signal beam is returned to the optical fiber coupler 5 in the original path, the second light beam is processed by the probe imaging module 9 and images a sample to obtain a sample signal beam with a confocal scanning imaging effect, the sample signal beam is returned to the optical fiber coupler 5 in the original path, the reference signal beam and the sample signal beam respectively return to the wavelength division multiplexer 3 and the b port and the c port of the optical fiber circulator 4 after interfering in the optical fiber coupler 5, finally, an interference signal is detected and collected by the comprehensive control processing module 20, and the comprehensive control processing module 20 performs processing operation on the interference signal to rapidly generate a three-dimensional image with a certain depth and a transverse section image with a specific depth.
In this technical solution, the OCT structure is used as a main body of the host module 19, and as long as the OCT structure portion in the host module 19 conforms to the structural features of the conventional OCT interferometer, the structure of the imaging system of both time-domain OCT and spectral OCT should be included in the protection scope of this technical solution.
Specifically, the splitting ratio of the fiber coupler 5 is 10:90, it is used for guiding the accurate positioning of the light source to the observed position, transmits the light beam of the sweep frequency light source at the same time, facilitate this optics coherent confocal microscopy endoscope system to carry on the scanning imaging to the area confirmed.
Specifically, the typical central wavelength of the swept-frequency light source 2 can be 840nm, 1310nm, 1550nm and the like, the bandwidth is greater than 50nm, and the long-wave band can perform accurate scanning on a tissue mucosa sample at a larger depth.
Specifically, the reference arm includes an optical fiber polarization controller 11, a first collimating lens 12, a focusing lens 13, and an optical delay line 14, the first light beam is modulated by the optical fiber polarization controller 11, so that the polarization state of the light beam is optimized, the polarization state of the first light beam is matched with the polarization state of the second light beam, and then the first light beam, the focusing lens 13, and the optical delay line 14 sequentially pass through the first collimating lens 12, the focusing lens 13, and the optical delay line 14 to form a reference signal light beam and return the reference signal light beam to the optical fiber coupler 5 in the original path, and the optical delay line 14 can adjust the optical path in real time, so that the optical path matching between the first light beam and the second light beam is realized.
Specifically, the probe imaging module 9 includes a second collimating lens 901, an MEMS micro-galvanometer 902, a scanning lens 903, a double cemented lens 904 and a microscope objective 905, the second light beam exits through the second collimating lens 901 inside the probe and enters the MEMS micro-galvanometer 902, the scanning lens 903 and the double cemented lens 904, and finally the second light beam images the sample through the microscope objective 905 to obtain a sample signal beam with a confocal scanning imaging effect, and the sample signal beam returns to the optical fiber coupler 5 in the original path; the MEMS micro-vibration mirror 902 can control the deflection angle of a light beam, realizes light beam scanning by controlling the drive voltage waveform, and has small mirror surface size and packaging size, thereby being beneficial to endoscopic imaging; the scanning lens 903 and the double cemented lens 904 are designed to form an optical 4F system to modulate the light beam, and in order to make the fiber diameter act as a confocal pinhole, the following relation is required between the focal lengths of the scanning lens 903 and the double cemented lens 904:
The focal length of the scanning lens 903 is f2, the focal length of the double-cemented lens 904 is f3, the numerical aperture of the microscope objective 905 is NA, and the fiber diameter of the single-mode fiber is d.
The technical solution does not limit the probe imaging module 9 to adopt the above structure, as long as the probe imaging module 9 can realize the function of confocal scanning imaging effect, and all are within the protection scope of the technical solution, as shown in fig. 2, the probe imaging module 9 includes a protection sleeve 906, a cavity 907, piezoelectric ceramics 908, a double cemented lens 909 and a microscope objective 910, the second light beam sequentially passes through the cavity 907, the piezoelectric ceramics 908 and the double cemented lens 909, and finally images the sample through the microscope objective 910 to obtain a sample signal light beam with confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler 5 in a primary path; piezoelectric ceramics 908 can be driven by voltage to adjust two shafts, single-mode optical fibers are driven to vibrate, light beam scanning is achieved, the two-shaft movement of the optical fibers also replaces the effect of a scanning lens 903, the structure is more compact, and the confocal scanning imaging effect is achieved.
Specifically, the integrated control processing module 20 includes a balance detector 16 for detecting interference signals, an acquisition card 17 for acquiring the interference signals detected by the balance detector 16, and a processing module 18 for processing and calculating the interference signals acquired by the acquisition card 17 and obtaining images, where the balance detector 16 is connected to the wavelength division multiplexer 3 and the c port of the light circulator 4 through single-mode optical fibers; the acquisition card 17 is connected with the sweep frequency light source 2, and the sweep frequency light source 2 outputs a clock and a trigger signal for controlling the acquisition card 17 to acquire an interference signal of a specific period output by the balanced detector 16; the processing module 18 is respectively connected with the MEMS micro-galvanometer 902 and the optical delay line 14, and the processing module 18 respectively controls the MEMS micro-galvanometer 902 and the optical delay line 14, and is used for adjusting the scanning and imaging ranges in combination with the positioning of the guiding light source. Because of the functions of the confocal structure and the coherence Gate (interference of the reference signal beam and the sample signal beam in the fiber coupler 5) in the probe imaging module 9, the system acquires a point intensity signal that does not need to be dyed, and can detect signals at different depths through the wavelength change of the swept-frequency light source 2, after the Processing module 18 acquires a signal of a complete galvanometer cycle, the FFT (Fast fourier transform) operation, interpolation zero-padding, spectral filtering, and subsequent image optimization Processing are realized by using GPU (Graphics Processing Unit) or PFGA (Field Programmable Gate Array) hardware, a three-dimensional image with a certain depth can be quickly generated, a transverse cross-sectional image with a certain depth is intercepted by software as an image of the OCM, a voltage value can be directly stored in the GPU or FPGA, a calculated transverse cross-sectional result is directly output, the operation rate is improved, the image has the advantages of simultaneous adjustment of the OCT and the OCT, the image can be adjusted to the real-time feedback Processing module according to the advantages of optical delay imaging, and the feedback of the closed-loop imaging 14.
In the technical scheme, after a sample signal beam and a reference signal beam with equal optical path difference interfere in an optical fiber coupler 5, the sample signal beam returns to a wavelength division multiplexer 3 and a port b and a port c of an optical fiber circulator 4, finally, a balance detector 16 detects interference signals, a sweep frequency light source 2 belongs to a wide-spectrum low-coherence light source, interference can only occur in a very short range due to the existence of a coherence gate, so that the signals have very high longitudinal resolution, due to the existence of a 4F system and a confocal structure, a confocal pinhole effect is achieved through an optical fiber aperture, most of defocused information is filtered, focus information is highlighted, and the signals also have very high transverse resolution, so that um-level three-dimensional scanning can be performed on a non-dyed sample.
As shown in fig. 3, an implementation method of the optical coherence confocal endomicroscopy system described above specifically includes the following steps:
step S100: guiding a light source beam emitted by a light source 1 to reach an optical fiber coupler 5 through single-mode optical fiber coupling and conduction of a wavelength division multiplexer 3; light source beams emitted by the sweep frequency light source 2 are transmitted to the optical fiber coupler 5 through the port a and the port b of the optical fiber circulator 4 in sequence;
step S200: the two light source beams are divided into two paths at the optical fiber coupler 5, and a first light beam and a second light beam are respectively arranged;
step S300: the first light beam is processed by the reference arm to form a reference signal light beam and returns to the optical fiber coupler 5 in the original path; the second light beam is processed by the probe imaging module 9 and images the sample to obtain a sample signal light beam with confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler 5 in the original path;
step S400: the reference signal beam and the sample signal beam interfere in the optical fiber coupler 5, and interference optical signals respectively return to ports b and c of the wavelength division multiplexer 3 and the optical fiber circulator 4;
step S500: interference light signals in the wavelength division multiplexer 3 and the optical fiber circulator 4 are detected by the balance detector 16, the sweep frequency light source 2 controls the acquisition card 17 to acquire interference signals of a specific period output by the balance detector 16, and the processing module 18 processes and operates the interference signals acquired by the acquisition card 17 to obtain a three-dimensional image with a certain depth and a transverse section image with a specific depth.
By the optical coherence confocal microscopy endoscope system and the implementation method thereof, the technical scheme can realize high-resolution, dyeing-free three-dimensional imaging of a sample, the imaging result can be transversely similar to a confocal effect, the longitudinal resolution is higher than that of OCT, the medical diagnosis result of sensitivity and specificity can be improved for medical imaging, and meanwhile, the system can be integrated and shared with the existing medical endoscope, so that accurate diagnosis is convenient.
Compared with the prior art, the technical scheme has the following advantages:
(1) By adopting the host module 19 taking an OCT structure as a main body and arranging the optical 4F system in the probe imaging module 9, the OCT and confocal resolution effect can be simultaneously achieved in one set of system, the real-time high-resolution three-dimensional imaging of a non-dyed sample can be carried out, and the provided horizontal OCM atlas can carry out high-sensitivity and specific medical diagnosis;
(2) The probe imaging module 9 of the technical scheme overcomes the defects of complex structure and longer light path of the existing probe, has small and compact structure, can perform scanning positioning and imaging simultaneously, and is beneficial to being used in an endoscope;
(3) According to the technical scheme, signals output by a balance detector 16 in the system are processed through system closed loop feedback, the optical delay line 14 is adjusted in real time according to imaging, a transverse OCM image with high resolution of a sample is output through the operation of a GPU or an FPGA, and a high-quality map which can be compared with a pathological section is provided.
According to the technical scheme, a section of 4F optical system is added at an OCT scanning imaging end, and the section of optical system is conveniently used in an endoscopic cavity channel, so that the aperture of a sample arm optical fiber is smaller than the minimum beam diameter (namely the minimum resolution of an objective lens) of an imaging surface, and the system has a confocal imaging effect; therefore, the resolution of OCT can be obviously improved while the imaging depth is not obviously reduced, the imaging effect similar to that of co-focusing is achieved under the condition of no dyeing, and the use of the MEMS micro-vibrating mirror and the calling of GPU/FPGA algorithm are combined and shared with the existing endoscope system in an integrated mode, so that the OCT imaging system becomes a medical diagnosis tool which is rapid, free of dyeing, high in sensitivity and specificity.
It is to be understood that the invention is not limited to the examples described above, but that modifications and variations may be effected thereto by those of ordinary skill in the art in light of the foregoing description, and that all such modifications and variations are intended to be within the scope of the invention as defined by the appended claims.
Claims (6)
1. An optically coherent confocal endomicroscopy system, comprising:
the system comprises a host module which takes a 0CT structure as a main body, wherein the host module comprises a guide light source, a wavelength division multiplexer, a sweep frequency light source, an optical fiber circulator, an optical fiber coupler and a reference arm;
the probe imaging module takes a confocal structure as a main body, obtains a sample interference signal by scanning a sample and has a confocal imaging effect;
the comprehensive control processing module is used for detecting and acquiring interference signals and processing and operating the acquired interference signals to obtain images;
the fiber circulator comprises three ports a, b and c which are arranged clockwise, and a guide light source and a wavelength division multiplexer, a port a of a sweep frequency light source and the fiber circulator, a wavelength division multiplexer and a fiber coupler, a port b of the fiber circulator and a fiber coupler, a fiber coupler and a reference arm, a fiber coupler and probe imaging module, a wavelength division multiplexer and a comprehensive control processing module, and a port c of the fiber circulator and a comprehensive control processing module are respectively connected through single mode fibers; the sweep frequency light source is connected with the comprehensive control processing module, and the sweep frequency light source controls the comprehensive control processing module to acquire interference signals; the comprehensive control processing module is respectively connected with the reference arm and the probe imaging module and controls the reference arm and the probe imaging module to adjust the scanning and imaging ranges; the guide light source emits a light source beam, and the light source beam is coupled by the single-mode fiber and transmitted by the wavelength division multiplexer to reach the fiber coupler; the sweep frequency light source emits a light source light beam, which is transmitted to the optical fiber coupler through the port a and the port b of the optical fiber circulator in sequence: two beams of light source beams are divided into a first beam and a second beam after passing through the optical fiber coupler, the first beam forms a reference signal beam after being processed by a reference arm and returns to the optical fiber coupler in the original path, the second beam is processed by the probe imaging module and images a sample to obtain a sample signal beam with a confocal scanning imaging effect, the sample signal beam returns to the optical fiber coupler in the original path, the reference signal beam and the sample signal beam return to a wavelength division multiplexer and a port b and a port c of an optical fiber circulator respectively after being interfered in the optical fiber coupler, finally, an interference signal is detected and collected by the comprehensive control processing module, the comprehensive control processing module processes and operates the interference signal to quickly generate a three-dimensional image with a certain depth and a transverse section image with a specific depth;
the reference arm comprises an optical fiber polarization controller, a first collimating lens, a focusing lens and an optical delay line, and the optical delay line is connected with the comprehensive control processing module and is controlled by the comprehensive control processing module; the first light beam is modulated by the optical fiber polarization controller to enable the polarization state of the first light beam to be matched with that of the second light beam, then the first light beam sequentially passes through the first collimating lens, the focusing lens and the optical delay line, the optical delay line adjusts the optical path of the first light beam in real time to enable the optical path of the first light beam to be matched with that of the second light beam, and finally a reference signal light beam is formed and returns to the optical fiber coupler in the original path;
the probe imaging module comprises a second collimating lens, an MEMS micro-vibration mirror for controlling the deflection angle of a light beam, a scanning lens, a double-cemented lens and a microscope objective, wherein the scanning lens and the double-cemented lens are designed to form an optical 4F system structure for modulating the light beam, and the MEMS micro-vibration mirror is connected with the comprehensive control processing module and is controlled by the comprehensive control processing module; and the second light beam is emitted through the second collimating lens, enters the MEMS micro-vibration lens, the scanning lens and the double-cemented lens in sequence, and finally images the sample through the micro-objective lens to obtain a sample signal light beam with a confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler in the original way.
2. The optical coherence confocal endomicroscopy system of claim 1, wherein the focal lengths of the scanning lens and the double cemented lens satisfy the following relationship:
Wherein f2 is the focal length of the scanning lens, f3 is the focal length of the double-cemented lens, NA is the numerical aperture of the microscope objective, and d is the fiber diameter of the single-mode fiber.
3. The optical coherence confocal endomicroscopy system of claim 1, wherein the probe imaging module comprises a protective sleeve, a cavity, a piezoelectric ceramic, a double-cemented lens and a microobjective, the piezoelectric ceramic is driven by voltage to perform two-axis adjustment to drive a single-mode optical fiber to vibrate to realize light beam scanning; the second light beam sequentially passes through the cavity, the piezoelectric ceramic and the double-cemented lens, and finally images the sample through the microscope objective to obtain a sample signal light beam with a confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler in the original path.
4. The optical coherence confocal microscopy endoscope system according to claim 1, wherein the comprehensive control processing module comprises a balance detector for detecting interference signals, an acquisition card for acquiring the interference signals detected by the balance detector and a processing module for processing and operating the interference signals acquired by the acquisition card and obtaining images, wherein the balance detector is respectively connected with the wavelength division multiplexer and a c port of the light circulator through single mode optical fibers; the acquisition card is connected with the sweep frequency light source, the sweep frequency light source outputs a clock and a trigger signal, and the acquisition card is controlled to acquire the interference signal of a specific period output by the balance detector: the processing module is respectively connected with the probe imaging module and the reference arm, and the processing module respectively controls the probe imaging module and the reference arm, and adjusts the scanning and imaging ranges by combining the positioning of the guide light source.
5. An implementation method of an optical coherence confocal endomicroscopy system, which is applied to the optical coherence confocal endomicroscopy system of any one of claims 1 to 4, and specifically comprises the following steps:
step S100: guiding light source beams emitted by a light source to reach the optical fiber coupler through single-mode optical fiber coupling and transmission of a wavelength division multiplexer; light source beams emitted by the sweep frequency light source are transmitted to the optical fiber coupler through the port a and the port b of the optical fiber circulator in sequence; step S200: the two light source light beams are divided into two paths at the optical fiber coupler, and the two light source light beams are respectively a first light beam and a second light beam;
step S300: the first light beam is processed by the reference arm to form a reference signal light beam and returns to the optical fiber coupler in the original path;
the second light beam is processed by the probe imaging module and images a sample to obtain a sample signal light beam with a confocal scanning imaging effect, and the sample signal light beam returns to the optical fiber coupler in the original path;
step S400: the reference signal beam and the sample signal beam interfere in the optical fiber coupler, and interference optical signals respectively return to a port b and a port c of the wavelength division multiplexer and the optical fiber circulator;
step S500: interference light signals in the wavelength division multiplexer and the optical fiber circulator are detected by the balance detector, the sweep frequency light source controls the acquisition card to acquire interference signals of a specific period output by the balance detector, and the processing module processes and operates the interference signals acquired by the acquisition card to obtain a three-dimensional image with a certain depth and a transverse section image with a specific depth.
6. The method for implementing an optically coherent confocal endomicroscopy system according to claim 5, wherein in the step S500: after acquiring an interference signal of a complete galvanometer cycle from an acquisition card, a processing module realizes FFT (fast Fourier transform algorithm) operation, interpolation zero filling, frequency spectrum filtering and subsequent image optimization processing through GPU (graphics processing Unit) or FGA (fast Fourier transform algorithm) hardware, quickly generates a three-dimensional image with a certain depth, and intercepts a transverse sectional view with a specific depth as an image of 0CM (0 CM); or the processing module directly stores the voltage value in the GPU or FPGA after acquiring an interference signal of a complete galvanometer cycle from the acquisition card, and directly outputs the calculated transverse section result as a 0CM image.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710542960.4A CN107328743B (en) | 2017-07-05 | 2017-07-05 | Optical coherent confocal microscopy endoscope system and implementation method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710542960.4A CN107328743B (en) | 2017-07-05 | 2017-07-05 | Optical coherent confocal microscopy endoscope system and implementation method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN107328743A CN107328743A (en) | 2017-11-07 |
| CN107328743B true CN107328743B (en) | 2023-03-28 |
Family
ID=60196817
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201710542960.4A Active CN107328743B (en) | 2017-07-05 | 2017-07-05 | Optical coherent confocal microscopy endoscope system and implementation method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN107328743B (en) |
Families Citing this family (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN108174122A (en) * | 2017-11-28 | 2018-06-15 | 武汉华之洋科技有限公司 | A kind of multiplex image acquisition device and method based on Fibre Optical Sensor |
| CN108490597A (en) * | 2018-06-05 | 2018-09-04 | 张红明 | A kind of confocal microscope system based on fiber coupler |
| CN108937842A (en) * | 2018-07-09 | 2018-12-07 | 执鼎医疗科技（杭州）有限公司 | A kind of OCT system integrating confocal fundus imaging |
| CN109008940A (en) * | 2018-07-09 | 2018-12-18 | 执鼎医疗科技（杭州）有限公司 | A kind of OCT system of the confocal fundus imaging of multiple light courcess |
| CN109045490B (en) * | 2018-08-22 | 2020-11-10 | 北京博纵科技有限公司 | Ultrasonic and skin quantification integrated beautifying system |
| CN109045489B (en) * | 2018-08-22 | 2021-05-14 | 北京博纵科技有限公司 | Adjustable ultrasonic beauty imaging system for deep skin and acquisition method thereof |
| CN109656014B (en) * | 2019-01-31 | 2024-03-19 | 北京超维景生物科技有限公司 | Multipath fluorescence collection device and three-dimensional nonlinear laser scanning cavity endoscope |
| CN110584615A (en) * | 2019-10-15 | 2019-12-20 | 南方科技大学 | Bimodal endoscopic imaging system |
| CN110801206B (en) * | 2019-11-18 | 2022-04-26 | 佛山光微科技有限公司 | Image correction method of high-resolution optical coherence confocal microscope |
| CN111053531A (en) * | 2019-11-20 | 2020-04-24 | 南京理工大学 | Handheld oral angiography device and method based on sweep frequency optical coherence tomography |
| FR3103894A1 (en) * | 2019-12-03 | 2021-06-04 | Damae Medical | Line scanning microscopy devices and methods |
| CN113349708B (en) * | 2021-06-08 | 2023-05-26 | 之江实验室 | Bimodal high-resolution large-depth microscopic endoscopic imaging system based on large-dispersion lens |
Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101032390A (en) * | 2007-03-29 | 2007-09-12 | 浙江大学 | Endoscopic imaging system in bulk optics biopsy spectral coverage OCT |
| CN201019719Y (en) * | 2007-03-29 | 2008-02-13 | 浙江大学 | Spectrum region OCT endoscopic image pick-up device used for in situ optical biopsy |
| CN102028454A (en) * | 2010-10-26 | 2011-04-27 | 浙江大学 | Mirror-image separation method and system based on group delay wavenumber carrier frequency |
| CN102525382A (en) * | 2012-02-08 | 2012-07-04 | 中国科学院光电技术研究所 | Helical scanning common path interference type endoscopic frequency-swept OCT (Optical Coherence Tomography) real-time imaging method and helical scanning common path interference type endoscopic frequency-swept OCT real-time imaging system |
| CN102818768A (en) * | 2012-07-31 | 2012-12-12 | 苏州微清医疗器械有限公司 | Multifunctional biomedical microscope |
| CN103815868A (en) * | 2014-02-26 | 2014-05-28 | 中国科学院光电技术研究所 | Full-eye optical coherence tomography imager |
| CN104545772A (en) * | 2014-12-19 | 2015-04-29 | 佛山市南海区欧谱曼迪科技有限责任公司 | Composite narrowband imaging endoscope imaging system |
| CN105054901A (en) * | 2015-08-26 | 2015-11-18 | 张文保 | Single-optical-fiber endoscope system integrated with optical coherence tomography and fractional flow reserve detection |
| CN105640480A (en) * | 2016-04-11 | 2016-06-08 | 佛山市南海区欧谱曼迪科技有限责任公司 | Motion adaptive common-path OCT endoscope system |
-
2017
- 2017-07-05 CN CN201710542960.4A patent/CN107328743B/en active Active
Patent Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101032390A (en) * | 2007-03-29 | 2007-09-12 | 浙江大学 | Endoscopic imaging system in bulk optics biopsy spectral coverage OCT |
| CN201019719Y (en) * | 2007-03-29 | 2008-02-13 | 浙江大学 | Spectrum region OCT endoscopic image pick-up device used for in situ optical biopsy |
| CN102028454A (en) * | 2010-10-26 | 2011-04-27 | 浙江大学 | Mirror-image separation method and system based on group delay wavenumber carrier frequency |
| CN102525382A (en) * | 2012-02-08 | 2012-07-04 | 中国科学院光电技术研究所 | Helical scanning common path interference type endoscopic frequency-swept OCT (Optical Coherence Tomography) real-time imaging method and helical scanning common path interference type endoscopic frequency-swept OCT real-time imaging system |
| CN102818768A (en) * | 2012-07-31 | 2012-12-12 | 苏州微清医疗器械有限公司 | Multifunctional biomedical microscope |
| CN103815868A (en) * | 2014-02-26 | 2014-05-28 | 中国科学院光电技术研究所 | Full-eye optical coherence tomography imager |
| CN104545772A (en) * | 2014-12-19 | 2015-04-29 | 佛山市南海区欧谱曼迪科技有限责任公司 | Composite narrowband imaging endoscope imaging system |
| CN105054901A (en) * | 2015-08-26 | 2015-11-18 | 张文保 | Single-optical-fiber endoscope system integrated with optical coherence tomography and fractional flow reserve detection |
| CN105640480A (en) * | 2016-04-11 | 2016-06-08 | 佛山市南海区欧谱曼迪科技有限责任公司 | Motion adaptive common-path OCT endoscope system |
Also Published As
| Publication number | Publication date |
|---|---|
| CN107328743A (en) | 2017-11-07 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN107328743B (en) | Optical coherent confocal microscopy endoscope system and implementation method | |
| US11083375B2 (en) | Handheld device for identification of microbiological constituents in the middle ear | |
| US7474407B2 (en) | Optical coherence tomography with 3d coherence scanning | |
| US8366271B2 (en) | Systems and methods for surgical microscope and optical coherence tomography (OCT) imaging | |
| JP4555074B2 (en) | Apparatus for imaging an object and apparatus for delivering low coherence optical radiation | |
| US8115934B2 (en) | Device and method for imaging the ear using optical coherence tomography | |
| CN105147241B (en) | Method and system based on double space carrier frequency technique extension OCT image depth | |
| US20110282192A1 (en) | Multimodal depth-resolving endoscope | |
| CN104545772B (en) | A kind of combined type Narrow-Band Imaging endoscopic imaging system | |
| JP2005529322A5 (en) | ||
| CN101791213A (en) | Optical tomographic imaging apparatus | |
| US10337995B2 (en) | Systems and methods for oblique laser scanning | |
| US20110273721A1 (en) | Novel compact, affordable optical test, measurement or imaging device | |
| WO2023088100A1 (en) | Multi-modal imaging apparatus based on raman spectrum and optical coherence tomography | |
| CN112493982A (en) | OCT structure and blood flow imaging's device in art | |
| CN104586344B (en) | A kind of multi-mode hysteroscope system and its implementation | |
| Aguirre et al. | Optical coherence microscopy | |
| CN110013212B (en) | Multi-parameter and multi-functional eye measuring instrument based on optical coherence tomography | |
| Mao et al. | Fiber lenses for ultra-small probes used in optical coherent tomography | |
| Vega et al. | Triple-modality co-registered endoscope featuring wide-field reflectance imaging, and high-resolution multiphoton and optical coherence microscopy | |
| Feng et al. | Lensless fiber imaging with long working distance based on active depth measurement | |
| CN201055372Y (en) | Rigid pipe type common-path type endoscopic OCT parallel imaging system | |
| Fujimoto et al. | Optical coherence tomography | |
| CN206920338U (en) | A kind of optical coherence confocal microscopy endoscope system | |
| Fujimoto | Optical coherence tomography: principles and applications |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CP03 | Change of name, title or address | ||
| CP03 | Change of name, title or address |
Address after: 528253 Room 503, Floor 5, Building A, Jingu Zhichuang Industrial Community, No. 2, Yong'an North Road, Dawu Community, Guicheng Street, Nanhai District, Foshan City, Guangdong Province (residence declaration) Patentee after: Guangdong Oupu Mandi Technology Co.,Ltd. Address before: Room 504-2, Floor 5, Building A, Jingu Optoelectronic Industry Community, No. 1, Pingzhou Yong'an North Road, Guicheng Street, Nanhai District, Foshan City, Guangdong Province, 528200 Patentee before: GUANGDONG OPTOMEDIC TECHNOLOGY CO.,LTD. |