CN112587085A - Optical coherent imaging system - Google Patents
Optical coherent imaging system Download PDFInfo
- Publication number
- CN112587085A CN112587085A CN202110238964.XA CN202110238964A CN112587085A CN 112587085 A CN112587085 A CN 112587085A CN 202110238964 A CN202110238964 A CN 202110238964A CN 112587085 A CN112587085 A CN 112587085A
- Authority
- CN
- China
- Prior art keywords
- image
- unit
- optical
- imaging system
- coherent
- 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.)
- Pending
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
Abstract
The invention is suitable for the field of medical instruments, and discloses an optical coherent imaging system which is characterized by comprising a broadband light source, a frequency sweep light source, a first interferometer, a second interferometer, a first optical fiber coupler, a second optical fiber coupler, a reference beam guiding unit, an image beam guiding unit, a spectrometer unit, a balance detection unit, an image analysis processing unit and a control unit.
Description
Technical Field
The invention relates to the field of medical instruments, in particular to an optical coherent imaging system.
Background
The optical coherence tomography has the characteristics of non-contact, no radiation, high detection sensitivity and no damage, and becomes a standard technology for measuring the human eye structure in the ophthalmic surgery. Preoperatively, the imaging system may generate and display an in-depth curved or cross-sectional reference image of the anterior segment of the eye, including the cornea, anterior chamber, and lens. A femtosecond laser assisted ophthalmic surgery is an ophthalmic surgery which is realized by utilizing femtosecond laser pulse, high-precision detection of an optical coherence tomography technology and precise calculation of a computer to plan a track and automatically and intelligently realize a plurality of key steps in the traditional ophthalmic surgery.
In conventional femtosecond laser assisted ophthalmic surgery, if the post-injury capsular sac may be damaged due to inaccurate measurement data, the vitreous humor overflows. Or as the femtosecond laser is not thorough in nucleus breaking, part of crystal epithelial cells can be remained in the capsular bag after ultrasonic emulsification, and the remained crystal epithelial cells grow on the surface of the posterior capsular sac of the crystal to cause the posterior capsular opacification and obviously shield light from entering the eyeball along the visual axis, so that the postoperative obvious vision of a patient is reduced, and then postoperative cataract is caused.
Moreover, various errors exist in the operation: the laser controller may miscalculate the position of the laser pulse for a variety of reasons, including optical aberrations, manufacturing tolerance issues with the laser, incorrect characterization of the refractive properties of the lens, pre-operative diagnostic errors, movement or property changes of the eye, and thermal creep of the component; the eye is a dynamic system, the entire lens can change over time due to the vitreous pressure difference in the anterior and posterior chambers behind the lens; lens curvature changes due to surgical accommodation, and so on.
Therefore, there is an urgent need to develop an optical imaging system, which can simultaneously realize the imaging of human eye structures with wide range and high precision, thereby realizing high-precision detection before operation, real-time imaging of whole eyes during operation, and improving the accuracy and safety of the operation.
Disclosure of Invention
The invention aims to provide an optical coherent imaging system, which aims to solve the technical problem that the prior art cannot give consideration to both depth and high-resolution human eye structure imaging.
In order to achieve the purpose, the invention provides the following scheme:
an optical coherent imaging system comprises a broadband light source, a swept-frequency light source, a first interferometer, a second interferometer, a first optical fiber coupler, a second optical fiber coupler, a reference beam guiding unit, an image beam guiding unit, a spectrometer unit, a balance detection unit, an image analysis processing unit and a control unit;
a scanning wavelength beam emitted by the broadband light source is divided into a first image beam and a first reference beam through a first interferometer, the first reference beam is sequentially transmitted to the first optical fiber coupler and the reference beam guiding unit through optical fibers, the reference beam guiding unit returns a second reference beam, the first image beam is sequentially transmitted to the second optical fiber coupler and the image beam guiding unit through the optical fibers, the image beam guiding unit transmits the first image beam to an eye, and light reflected and scattered by the eye is a second image beam;
the second reference beam and the second image beam are subjected to coherence at the first interferometer to generate first coherent light, the first coherent light is transmitted to the spectrometer unit, the spectrometer unit performs spectral analysis on the first coherent light to obtain spectral information, and transmits the obtained spectral information to the image analysis processing unit;
the scanning wavelength beam emitted by the swept-frequency light source is divided into a third image beam and a third reference beam through the second interferometer, the third reference beam is sequentially transmitted to the first optical fiber coupler and the reference beam guiding unit through optical fibers, the reference beam guiding unit returns a fourth reference beam, the third image beam is sequentially transmitted to the second optical fiber coupler and the image beam guiding unit through the optical fibers, the image beam guiding unit transmits the third image beam to the eye, and light reflected and scattered by the eye is a fourth image beam;
the fourth reference beam and the fourth image beam are coherent at a second interferometer to generate second coherent light, the second coherent light is transmitted to the balance detection unit, the balance detection unit receives the second coherent light, the balance detection unit performs data generation on the second coherent light to obtain a data signal, and the obtained data signal is transmitted to the image analysis processing unit;
the image analysis processing unit analyzes and processes the spectrum information transmitted by the spectrometer unit and the data signal transmitted by the balance detection unit and generates image information;
the control unit generates an operation signal of an operation target area according to the image information generated by the image analysis processing unit.
Preferably, the spectrometer unit comprises a first collimating lens, a first beam splitting grating, a second collimating lens, a second beam splitting grating, a first focusing lens, a sensor and a first photoelectric converter which are arranged along the optical path in sequence, the first coherent light is incident to the first collimating lens to form first parallel light, the first parallel light is incident to the first light splitting grating to perform first-order light splitting to form first-order light splitting beams, the first-order splitting light beam is incident to the second collimating lens to form second parallel light, the second parallel light is incident to the second splitting grating to perform second-order splitting to form a second-order splitting light beam, the secondary split light beam is focused on a sensor through a first focusing lens, the sensor acquires spectral information, and transmitting the acquired spectral information to a first photoelectric converter, wherein the first photoelectric converter converts the acquired spectral information into an electric signal and transmits the electric signal to an image analysis processing unit.
Preferably, the reference beam guiding unit includes a third collimating lens, a fourth collimating lens, a second focusing lens, a reflecting mirror and a voice coil motor, the third collimating lens, the fourth collimating lens, the second focusing lens and the reflecting mirror are sequentially connected through an optical fiber, the reflecting mirror is disposed on the voice coil motor, and the voice coil motor is used for adjusting a distance between the reflecting mirror and the second focusing lens.
Preferably, the image beam guiding unit includes a fifth collimating lens, a 2D scanning unit, and a third focusing lens, which are sequentially connected by an optical fiber.
Preferably, the balance detection unit includes a balance detector, a data analyzer, and a second photoelectric converter, the balance detector performs heterodyne detection on a second coherent optical signal and transmits the second coherent optical signal to the data analyzer, the data analyzer is configured to analyze the second coherent optical signal transmitted by the balance detector and form a data signal, the second photoelectric converter receives the data signal transmitted by the data analyzer, and the second photoelectric converter converts the data signal into an electrical signal and transmits the electrical signal to the image analysis processing unit.
Preferably, the center wavelength of the broadband light source is 840nm, and the center wavelength of the swept-frequency light source is 1310 nm.
Preferably, the imaging depth of the optical coherent imaging system is 7mm-10mm, and the imaging resolution of the optical coherent imaging system is 5-7.5 μm.
Preferably, the imaging time of the optical coherence imaging system is 0.01-0.1 seconds.
Preferably, the frame rate of the optical coherence imaging system is 50-100 frames/sec.
The optical coherent imaging system provided by the invention adopts the broadband light source and the sweep frequency light source as the scanning light source, can give consideration to both high resolution and large imaging depth, solves the problem that the prior art cannot give consideration to both depth and high-resolution human eye structure imaging, can realize preoperative high-precision detection and intraoperative whole-eye real-time imaging, and can improve the accuracy and safety of the operation.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the structures shown in the drawings without creative efforts.
Fig. 1 is a schematic structural diagram of an optical coherence imaging system provided in an embodiment of the present invention.
The reference numbers illustrate:
1. a broadband light source; 2. sweeping a light source; 3. a first interferometer; 4. a second interferometer; 5. a first fiber coupler; 6. a second fiber coupler; 7. a reference beam guiding unit; 71. a third collimating lens; 72. a fourth collimating lens; 73. a second focusing lens; 74. a mirror; 75. a voice coil motor; 8. an image beam guiding unit; 81. a fifth collimating lens; 82. a 2D scanning unit; 83. a third focusing lens; 9. a spectrometer unit; 91. a first collimating lens; 92. a first beam splitting grating; 93. a second collimating lens; 94. a second beam splitting grating; 95. a first focusing lens; 96. a sensor; 97. a first photoelectric converter; 10. a balance detection unit; 101. a balance detector; 102. a data analyzer; 103. a second photoelectric converter; 11. an image analysis processing unit; 12. a control unit.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
It should be noted that all the directional indicators (such as up, down, left, right, front, and rear … …) in the embodiment of the present invention are only used to explain the relative position relationship between the components, the movement situation, etc. in a specific posture (as shown in the drawing), and if the specific posture is changed, the directional indicator is changed accordingly.
It will also be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present.
In addition, the descriptions related to "first", "second", etc. in the present invention are for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In addition, technical solutions between various embodiments may be combined with each other, but must be realized by a person skilled in the art, and when the technical solutions are contradictory or cannot be realized, such a combination should not be considered to exist, and is not within the protection scope of the present invention.
Referring to fig. 1, an optical coherence imaging system according to an embodiment of the present invention includes a broadband light source 1, a swept-frequency light source 2, a first interferometer 3, a second interferometer 4, a first fiber coupler 5, a second fiber coupler 6, a reference beam guiding unit 7, an image beam guiding unit 8, a spectrometer unit 9, a balance detecting unit 10, an image analyzing and processing unit 11, and a control unit 12. Wherein the content of the first and second substances,
the broadband light source 1 is used for generating a scanning long beam, the scanning wavelength beam emitted by the broadband light source 1 is divided into a first image beam and a first reference beam through the first interferometer 3, the first reference beam is sequentially transmitted to the first optical fiber coupler 5 and the reference beam guiding unit 7 through optical fibers, the reference beam guiding unit 7 returns a second reference beam, the first image beam is sequentially transmitted to the second optical fiber coupler 6 and the image beam guiding unit 8 through the optical fibers, the image beam guiding unit 8 transmits the first image beam to an eye, and light reflected and scattered by the eye is a second image beam;
the second reference beam and the second image beam are coherent at the first interferometer 3 to generate first coherent light, the spectrometer unit 9 receives the first coherent light, and the spectrometer unit 9 performs spectral analysis on the first coherent light to obtain spectral information and transmits the obtained spectral information to the image analysis processing unit 11.
The swept-frequency light source 2 is used for generating a scanning long beam, the scanning wavelength beam emitted by the swept-frequency light source 2 is divided into a third image beam and a third reference beam through the second interferometer 4, the third reference beam is sequentially transmitted to the first optical fiber coupler 5 and the reference beam guiding unit 7 through optical fibers, the reference beam guiding unit 7 returns the fourth reference beam, the third image beam is sequentially transmitted to the second optical fiber coupler 6 and the image beam guiding unit 8 through the optical fibers, the image beam guiding unit 8 transmits the third image beam to eyes, and light reflected and scattered by the eyes is the fourth image beam;
the fourth reference beam and the fourth image beam are coherent at the second interferometer 4 to generate second coherent light, the balance detection unit 10 receives the second coherent light, and the balance detection unit 10 performs data generation on the second coherent light to obtain a data signal and transmits the obtained data signal to the image analysis processing unit 11.
The image analysis processing unit 11 performs analysis processing on the spectrum information transmitted by the spectrometer unit 9 and the data signal transmitted by the balance detection unit 10, and generates image information.
The control unit 12 generates a surgical signal of the surgical target region from the image information generated by the image analysis processing unit 11.
The optical coherent imaging system of the embodiment of the invention adopts the broadband light source 1 and the sweep frequency light source 2 as scanning light sources, can give consideration to both high resolution and large imaging depth, solves the problem that the prior art can not give consideration to both depth and high-resolution human eye structure imaging, can realize preoperative high-precision detection and intraoperative whole-eye real-time imaging, and thus can improve the accuracy and safety of operations.
The broadband light source 1 imaging system and the sweep frequency light source 2 imaging system have the characteristics of imaging, the sweep frequency light source 2 imaging system has the characteristics of high scanning speed and large scanning depth, and can realize full-eye real-time dynamic imaging on a human eye structure, but the resolution ratio is not high. The broadband light source 1 imaging system has the characteristics of high resolution and high precision, can obtain full-eye three-dimensional image information with high resolution, high precision and high definition, and has insufficient imaging depth. Therefore, an optical coherent imaging system consisting of a broadband light source 1 imaging system and a sweep frequency light source 2 imaging system can be constructed, the sweep frequency light source 2 imaging system and the broadband light source 1 imaging system do not work independently, and a pair of structures which work in a coordinated mode are constructed between the two systems, so that the purposes of obtaining high-resolution and clear image information from an eye cornea to an eye fundus retina, accurately positioning femtosecond laser pulses in real time and formulating a new operation scheme according to the collected image information are achieved, high-precision detection before an operation is ensured, real-time three-dimensional imaging of the whole eye in the operation and real-time dynamic adjustment of the position of a femtosecond pulse laser beam focusing eye tissue are achieved.
Preferably, the center wavelength of the broadband light source 1 is 840nm, the center wavelength of the swept-frequency light source 2 is 1310nm, and the working bands of the center wavelengths of 840nm and 1310nm are fused for use, so that both high resolution and large imaging depth are achieved.
Preferably, the z-imaging range of the optical coherence imaging system is 4mm-8mm circumference.
It will be appreciated that the imaging system collects image data at (x, y) points in parallel from all z depths simultaneously, collects parallel or simultaneous attributes of image data from different depths, and generates a single image with a larger range by integrating adjacent depth images using complex image recognition and processing circuitry.
Preferably, the imaging time of the optical coherence imaging system is 0.01-0.1 seconds.
It will be appreciated that the present invention is fast imaging and short imaging time, meaning that images can be generated that provide timely and therefore useful feedback to the surgeon regarding the progress of the ophthalmic surgery so that the surgeon can modify the surgical procedure in response to the feedback, and can view in real time during the imaging of structures of the human eye. During the femtosecond laser-assisted ophthalmic surgery, a doctor can observe the surgical process of a patient in real time, simultaneously two optical coherence tomography measurement systems coordinate to image the human eye structure in real time, and the imaging of a three-dimensional model of the human eye structure and the observation of the surgical implementation process can be completed simultaneously.
Preferably, the frame rate of the optical coherence imaging system is 50-100 frames/sec.
It will be appreciated that a typical refresh rate used for live video images is about 24 frames/second. Thus, an imaging system providing images at a refresh rate or frame rate of 50-100 frames/second may provide high resolution live images to a physician. While systems with frame rates or refresh rates much less than 20 to 25 frames/second may not be considered live video imaging, but rather as unstable, jumpy images, possibly even distracting the physician from the ophthalmic surgery.
The imaging depth of the optical coherent imaging system is 7-10mm, and the imaging resolution of the optical coherent imaging system is 5-7.5 μm.
It can be understood that through the coordination work of the two coherent optical imaging systems, the imaging system of the sweep light source 2 can reach the imaging depth of 7-10mm, the whole eye image information from the cornea to the crystalline lens to the fundus retina can be acquired and imaged, and the imaging system of the broadband light source 1 can reach the imaging resolution of 5-7.5 μm, and can provide the image information of the whole eye with high definition. The problem of can't compromise degree of depth, the human eye structure formation of image of high resolution among the prior art is solved, can realize high accuracy detection before the art, the real-time formation of image of full eye in the art improves the accuracy nature and the security of operation.
Preferably, the spectrometer unit 9 includes a first collimating lens 91, a first beam splitting grating 92, a second collimating lens 93, a second beam splitting grating 94, a first focusing lens 95, a sensor 96 and a first photoelectric converter 97, which are sequentially disposed along the optical path, the first coherent light enters the first collimating lens 91 to form a first parallel light, the first parallel light enters the first beam splitting grating 92 to perform a first-order splitting to form a first-order split light beam (i.e. to split the spectrum into spectral content), the first-order split light beam enters the second collimating lens 93 to form a second parallel light, the second parallel light enters the second beam splitting grating 94 to perform a second-order splitting to form a second-order split light beam (i.e. to split the spectrum into spectral content), the second-order split light beam is focused onto the sensor 96 through the first focusing lens 95, the sensor 96 obtains the spectral information and transmits the obtained spectral information to the first photoelectric converter 97, the first photoelectric converter 97 converts the acquired spectral information into an electric signal and transmits the electric signal to the image analysis processing unit 11, and the spectrometer unit 9 is ingenious in structural design and high in accuracy.
Preferably, the balance detection unit 10 includes a balance detector 101, a data analyzer 102, and a second photoelectric converter 103, the balance detector 101 performs heterodyne detection on the second coherent optical signal and transmits the second coherent optical signal to the data analyzer 102, the data analyzer 102 is configured to analyze the second coherent optical signal transmitted by the balance detector 101 and form a data signal (i.e., a time series), the second photoelectric converter 103 receives the data signal (i.e., the time series) transmitted by the data analyzer 102, and the second photoelectric converter 103 converts the data signal (i.e., the time series) into an electrical signal and transmits the electrical signal to the image analysis processing unit 11.
It will be appreciated that heterodyne detection is performed in the balanced detector with the fourth reference beam reflected back via the reference beam guiding unit 7, thereby avoiding background noise effects caused by ambient temperature, humidity, vibrations, etc. of the reference beam guiding unit 7 and the image beam guiding unit 8. Because the detection depth of the sweep-frequency optical coherence tomography is large, and the scanning speed is high, the human eye three-dimensional structure model can be quickly reconstructed by using the data of the key position points of the human eye detected by the sweep-frequency optical coherence tomography, and the real-time tracking of the spatial pose of the human eye is realized.
The reference beam guiding unit 7 includes a third collimating lens 71, a fourth collimating lens 72, a second focusing lens 73, a reflecting mirror 74, and a voice coil motor 75, the third collimating lens 71, the fourth collimating lens 72, the second focusing lens 73, and the reflecting mirror 74 are sequentially connected through an optical fiber, the reflecting mirror 74 is disposed on the voice coil motor 75, and the voice coil motor 75 is used for adjusting a distance between the reflecting mirror 74 and the second focusing lens 73, in this embodiment, the voice coil motor 75 can linearly move in a micrometer scale.
It is understood that since the effective detection depth of the spectral domain optical coherence tomography is about 3mm, which is not enough to cover the detection of the entire lens and the anterior and posterior capsule by about 8mm, the mirror 74 and the voice coil motor 75 in the embodiment of the present invention constitute a spectral domain optical coherence tomography detection module with variable detection depth.
It is understood that the voice coil motor 75 compensates for the measurement error introduced by the human eye's vibration in the optical axis direction on the one hand by utilizing the high-speed dynamic response capability of the voice coil motor 75; on the other hand, the axial translation of the spectral domain optical coherence tomography detection range is completed by the one-dimensional direction movement of the voice coil motor 75.
Preferably, the image beam guiding unit 8 includes a fifth collimator lens 81, a 2D scanning unit 82, and a third focusing lens 83, which are sequentially connected by an optical fiber.
The above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention, and all modifications and equivalents of the present invention, which are made by the contents of the present specification and the accompanying drawings, or directly/indirectly applied to other related technical fields, are included in the scope of the present invention.
Claims (9)
1. An optical coherent imaging system is characterized by comprising a broadband light source, a swept-frequency light source, a first interferometer, a second interferometer, a first optical fiber coupler, a second optical fiber coupler, a reference beam guiding unit, an image beam guiding unit, a spectrometer unit, a balance detection unit, an image analysis processing unit and a control unit;
a scanning wavelength beam emitted by the broadband light source is divided into a first image beam and a first reference beam through a first interferometer, the first reference beam is sequentially transmitted to the first optical fiber coupler and the reference beam guiding unit through optical fibers, the reference beam guiding unit returns a second reference beam, the first image beam is sequentially transmitted to the second optical fiber coupler and the image beam guiding unit through the optical fibers, the image beam guiding unit transmits the first image beam to an eye, and light reflected and scattered by the eye is a second image beam;
the second reference beam and the second image beam are subjected to coherence at the first interferometer to generate first coherent light, the first coherent light is transmitted to the spectrometer unit, the spectrometer unit performs spectral analysis on the first coherent light to obtain spectral information, and transmits the obtained spectral information to the image analysis processing unit;
the scanning wavelength beam emitted by the swept-frequency light source is divided into a third image beam and a third reference beam through the second interferometer, the third reference beam is sequentially transmitted to the first optical fiber coupler and the reference beam guiding unit through optical fibers, the reference beam guiding unit returns a fourth reference beam, the third image beam is sequentially transmitted to the second optical fiber coupler and the image beam guiding unit through the optical fibers, the image beam guiding unit transmits the third image beam to the eye, and light reflected and scattered by the eye is a fourth image beam;
the fourth reference beam and the fourth image beam are coherent at a second interferometer to generate second coherent light, the second coherent light is transmitted to the balance detection unit, the balance detection unit receives the second coherent light, the balance detection unit performs data generation on the second coherent light to obtain a data signal, and the obtained data signal is transmitted to the image analysis processing unit;
the image analysis processing unit analyzes and processes the spectrum information transmitted by the spectrometer unit and the data signal transmitted by the balance detection unit and generates image information;
the control unit generates an operation signal of an operation target area according to the image information generated by the image analysis processing unit.
2. The optical coherence imaging system of claim 1, wherein the spectrometer unit comprises a first collimating lens, a first beam splitter grating, a second collimating lens, a second beam splitter grating, a first focusing lens, a sensor and a first photoelectric converter, which are sequentially disposed along an optical path, the first coherent light beam enters the first collimating lens to form a first parallel light beam, the first parallel light beam enters the first beam splitter grating to perform a first-order splitting to form a first-order split light beam, the first-order split light beam enters the second collimating lens to form a second parallel light beam, the second parallel light beam enters the second beam splitter grating to perform a second-order splitting to form a second-order split light beam, the second-order split light beam is focused onto the sensor by the first focusing lens, the sensor obtains spectral information and transmits the obtained spectral information to the first photoelectric converter, the first photoelectric converter converts the acquired spectral information into an electric signal and transmits the electric signal to the image analysis processing unit.
3. The optical coherence imaging system of claim 1, wherein the reference beam guiding unit comprises a third collimating lens, a fourth collimating lens, a second focusing lens, a mirror and a voice coil motor, the third collimating lens, the fourth collimating lens, the second focusing lens and the mirror are sequentially connected through an optical fiber, the mirror is disposed on the voice coil motor, and the voice coil motor is used for adjusting a distance between the mirror and the second focusing lens.
4. The optical coherence imaging system of claim 1, wherein the image beam directing unit comprises a fifth collimating lens, a 2D scanning unit and a third focusing lens connected in sequence by an optical fiber.
5. The optical coherence imaging system of claim 1, wherein the balanced detection unit comprises a balanced detector, a data analyzer and a second photoelectric converter, the balanced detector performs heterodyne detection on the second coherent optical signal and transmits the second coherent optical signal to the data analyzer, the data analyzer is configured to analyze the second coherent optical signal transmitted by the balanced detector and form a data signal, the second photoelectric converter receives the data signal transmitted by the data analyzer, and the second photoelectric converter converts the data signal into an electrical signal and transmits the electrical signal to the image analysis processing unit.
6. The optical coherence imaging system of claim 1, wherein the broadband light source has a central wavelength of 840nm and the swept-frequency light source has a central wavelength of 1310 nm.
7. The optical coherence imaging system of claim 1, wherein an imaging depth of the optical coherence imaging system is 7mm to 10mm and an imaging resolution of the optical coherence imaging system is 5 to 7.5 μm.
8. The optical coherence imaging system of claim 1, wherein an imaging time of the optical coherence imaging system is 0.01-0.1 seconds.
9. The optical coherence imaging system of claim 1, wherein a frame rate of the optical coherence imaging system is 50-100 frames/sec.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110238964.XA CN112587085A (en) | 2021-03-04 | 2021-03-04 | Optical coherent imaging system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110238964.XA CN112587085A (en) | 2021-03-04 | 2021-03-04 | Optical coherent imaging system |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN112587085A true CN112587085A (en) | 2021-04-02 |
Family
ID=75210251
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110238964.XA Pending CN112587085A (en) | 2021-03-04 | 2021-03-04 | Optical coherent imaging system |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN112587085A (en) |
Citations (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101019759A (en) * | 2007-03-14 | 2007-08-22 | 温州医学院 | Method of measuring eye axis length and live tissue structure thickness of animal |
| CN101248983A (en) * | 2008-04-08 | 2008-08-27 | 上海理工大学 | Compensating mechanism of human eyes wave-front optical aberration measurement and correct system |
| CN102119850A (en) * | 2011-03-07 | 2011-07-13 | 中国科学院光电技术研究所 | Triple differential confocal fundus retina scanning and imaging device and method on basis of adaptive optics |
| US20140218741A1 (en) * | 2012-12-31 | 2014-08-07 | Axsun Technologies, Inc. | OCT Swept Laser with Cavity Length Compensation |
| CN103976707A (en) * | 2014-05-20 | 2014-08-13 | 深圳市斯尔顿科技有限公司 | OCT (Optical Coherence Tomography) system for measuring optical path value of axis oculi and method |
| CN105761218A (en) * | 2016-02-02 | 2016-07-13 | 中国科学院上海光学精密机械研究所 | Optical coherence tomography image pseudo-color processing method |
| CN106063700A (en) * | 2016-05-24 | 2016-11-02 | 中国科学院长春光学精密机械与物理研究所 | Quickly catching and formation method of less than the 10 microns capillary vessel in optical fundus |
| JP2017009455A (en) * | 2015-06-23 | 2017-01-12 | 学校法人北里研究所 | Light source unit for optical interference tomography and optical interference tomographic device |
| CN106361279A (en) * | 2016-08-30 | 2017-02-01 | 中国科学院上海光学精密机械研究所 | Full-investigation depth dispersion compensation method by optical coherence tomography system |
| CN107064001A (en) * | 2017-02-28 | 2017-08-18 | 福建师范大学 | Monochromatic light spectrometer polarization domain optical coherence tomography system based on photoswitch |
| CN107126196A (en) * | 2017-05-18 | 2017-09-05 | 武汉理工大学 | Peeped in a kind of human body and monitor OCT medical systems and its preparation method of joint probe with real-time temperature and pressure |
| CN110292361A (en) * | 2019-07-30 | 2019-10-01 | 佛山科学技术学院 | A kind of dermal imaging apparatus and method for of super wide range |
| CN111265183A (en) * | 2020-02-19 | 2020-06-12 | 淮阴工学院 | Retina blood flow measuring device based on light beam parallel scanning mode |
| CN111366545A (en) * | 2020-04-09 | 2020-07-03 | 公安部物证鉴定中心 | Handheld dual-waveband common-path optical tomography imaging system |
-
2021
- 2021-03-04 CN CN202110238964.XA patent/CN112587085A/en active Pending
Patent Citations (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101019759A (en) * | 2007-03-14 | 2007-08-22 | 温州医学院 | Method of measuring eye axis length and live tissue structure thickness of animal |
| CN101248983A (en) * | 2008-04-08 | 2008-08-27 | 上海理工大学 | Compensating mechanism of human eyes wave-front optical aberration measurement and correct system |
| CN102119850A (en) * | 2011-03-07 | 2011-07-13 | 中国科学院光电技术研究所 | Triple differential confocal fundus retina scanning and imaging device and method on basis of adaptive optics |
| US20140218741A1 (en) * | 2012-12-31 | 2014-08-07 | Axsun Technologies, Inc. | OCT Swept Laser with Cavity Length Compensation |
| CN103976707A (en) * | 2014-05-20 | 2014-08-13 | 深圳市斯尔顿科技有限公司 | OCT (Optical Coherence Tomography) system for measuring optical path value of axis oculi and method |
| JP2017009455A (en) * | 2015-06-23 | 2017-01-12 | 学校法人北里研究所 | Light source unit for optical interference tomography and optical interference tomographic device |
| CN105761218A (en) * | 2016-02-02 | 2016-07-13 | 中国科学院上海光学精密机械研究所 | Optical coherence tomography image pseudo-color processing method |
| CN106063700A (en) * | 2016-05-24 | 2016-11-02 | 中国科学院长春光学精密机械与物理研究所 | Quickly catching and formation method of less than the 10 microns capillary vessel in optical fundus |
| CN106361279A (en) * | 2016-08-30 | 2017-02-01 | 中国科学院上海光学精密机械研究所 | Full-investigation depth dispersion compensation method by optical coherence tomography system |
| CN107064001A (en) * | 2017-02-28 | 2017-08-18 | 福建师范大学 | Monochromatic light spectrometer polarization domain optical coherence tomography system based on photoswitch |
| CN107126196A (en) * | 2017-05-18 | 2017-09-05 | 武汉理工大学 | Peeped in a kind of human body and monitor OCT medical systems and its preparation method of joint probe with real-time temperature and pressure |
| CN110292361A (en) * | 2019-07-30 | 2019-10-01 | 佛山科学技术学院 | A kind of dermal imaging apparatus and method for of super wide range |
| CN111265183A (en) * | 2020-02-19 | 2020-06-12 | 淮阴工学院 | Retina blood flow measuring device based on light beam parallel scanning mode |
| CN111366545A (en) * | 2020-04-09 | 2020-07-03 | 公安部物证鉴定中心 | Handheld dual-waveband common-path optical tomography imaging system |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US10702146B2 (en) | Angular multiplexed optical coherence tomography systems and methods | |
| US8690328B1 (en) | Methods and devices for ophthalmic optical tomographic image display | |
| US20050140981A1 (en) | Measurement of optical properties | |
| EP3273839B1 (en) | Multiple depth optical coherence tomography system and method and laser eye surgery system incorporating the same | |
| CN101346104B (en) | Ophthalmological measuring system and method for determining the biometric data of an eye | |
| US20090285354A1 (en) | Optical coherence tomographic imaging device and imaging method of optical coherence tomographic image | |
| JPH0866421A (en) | Ophthalmology operation device | |
| CN103961061B (en) | Optical tomographic imaging apparatus and control method thereof | |
| JPWO2006022342A1 (en) | Optical interference tomography light generator for biological tissue measurement and optical interference tomography device for biological tissue measurement | |
| US9161687B2 (en) | Device for interferometrically measuring the eye length and the anterior eye segment | |
| CN114903426B (en) | Comprehensive ophthalmic image system based on sweep source OCT and acquisition method thereof | |
| CN112587303B (en) | Laser eye surgery system based on dual-mode image adjustment | |
| US20050117117A1 (en) | Intraoperative biometry | |
| CN112244760A (en) | Imaging device for realizing function of anterior segment OCT integrated biological measuring instrument based on beam splitter prism | |
| CN112587304B (en) | Femtosecond laser guiding system and method based on dual-mode image | |
| CN112587084A (en) | Optical coherent imaging system with real-time adjustable imaging depth | |
| CN113229777B (en) | Visual quality analyzer | |
| CN112587085A (en) | Optical coherent imaging system | |
| EP2230990B1 (en) | Ophthalmic instrument alignment apparatus and method of using same | |
| CN114159020A (en) | Refractometer, ophthalmological biological multi-parameter measuring instrument and measuring method | |
| CN106963337A (en) | One kind realizes big depth of field eye anterior segment analysis system | |
| CN111163681B (en) | Phase sensitive optical coherence tomography to measure optical aberrations of the anterior segment | |
| DE102012011880A1 (en) | Contactless measuring device for ophthalmic calculation and selection of intraocular lenses, has keratometer arrangement that is provided for determining corneal curvature of eye | |
| EP4316351A1 (en) | Ophthalmic device and eye inspection method | |
| CN117547218A (en) | Optical system and method for measuring eye axis length |
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 | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20210402 |
|
| RJ01 | Rejection of invention patent application after publication |