CN111436907A - Cerebrovascular imaging device based on sweep frequency adaptive optics OCT - Google Patents
Cerebrovascular imaging device based on sweep frequency adaptive optics OCT Download PDFInfo
- Publication number
- CN111436907A CN111436907A CN202010303433.XA CN202010303433A CN111436907A CN 111436907 A CN111436907 A CN 111436907A CN 202010303433 A CN202010303433 A CN 202010303433A CN 111436907 A CN111436907 A CN 111436907A
- Authority
- CN
- China
- Prior art keywords
- coupler
- mirror
- sample
- detector
- control processor
- 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
- 238000003384 imaging method Methods 0.000 title claims abstract description 28
- 230000003044 adaptive effect Effects 0.000 title claims abstract description 26
- 239000013307 optical fiber Substances 0.000 claims abstract description 29
- 239000000835 fiber Substances 0.000 claims description 6
- 238000012545 processing Methods 0.000 claims description 4
- 239000002872 contrast media Substances 0.000 abstract description 6
- 238000012634 optical imaging Methods 0.000 abstract description 2
- 238000012014 optical coherence tomography Methods 0.000 description 16
- 230000003287 optical effect Effects 0.000 description 8
- 238000002583 angiography Methods 0.000 description 5
- 208000026106 cerebrovascular disease Diseases 0.000 description 4
- 238000003491 array Methods 0.000 description 3
- 238000010968 computed tomography angiography Methods 0.000 description 3
- 238000012937 correction Methods 0.000 description 3
- 230000006378 damage Effects 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 230000035945 sensitivity Effects 0.000 description 3
- 239000000243 solution Substances 0.000 description 3
- 238000003325 tomography Methods 0.000 description 3
- 208000027418 Wounds and injury Diseases 0.000 description 2
- 238000011161 development Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012360 testing method Methods 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 208000014674 injury Diseases 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 238000005459 micromachining Methods 0.000 description 1
- 238000005457 optimization Methods 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 230000002792 vascular Effects 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0066—Optical coherence imaging
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
- A61B5/004—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
- A61B5/0042—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part for the brain
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Biomedical Technology (AREA)
- Molecular Biology (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Physics & Mathematics (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Biophysics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Neurology (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
The invention relates to the technical field of optical imaging, in particular to a cerebrovascular imaging device based on sweep frequency adaptive optics OCT, which comprises: the device comprises a sweep frequency light source, an optical fiber coupler, a reference arm, a sample arm, a detector and a control processor; one end of the optical fiber coupler is respectively connected with the sweep frequency light source and the detector; the other end of the optical fiber coupler is respectively connected with the reference arm and the sample arm; the other end of the sample arm is over against a sample to be detected; the control processor is respectively connected with the detector and the sample arm; the cerebrovascular imaging device provided by the invention can greatly improve the system resolution and does not need contrast agents.
Description
Technical Field
The invention belongs to the technical field of optical imaging, and particularly relates to a cerebrovascular imaging device based on sweep-frequency adaptive Optical Coherence Tomography (OCT).
Background
Cerebrovascular diseases are serious diseases, the mortality rate and the disability rate are relatively high, and the development of advanced examination technology corresponding to the cerebrovascular diseases is very important.
Since its birth, optical tomography (OCT) has been widely used in biomedical imaging, and it features high imaging speed, high resolution and no damage to human body. OCT is also applied to angiography, becoming a new angiography technique: the optical tomography coherence tomography angiography imaging (OCTA), the Adaptive Optics (AO) and the OCT are combined, the resolution of equipment can be greatly improved, the technical performance of a sweep frequency light source (SS) is improved along with the development of hardware, the application of the sweep frequency OCT is also wide, compared with the traditional laser light source, the sweep frequency light source has good equipment sensitivity, and the depth information of the equipment can be better detected, and the sweep frequency adaptive optics OCT equipment (AO-SS-OCT) combining the adaptive optics and the sweep frequency OCT is used, on one hand, the resolution of the equipment can be greatly improved, on the other hand, the equipment can better detect the information at a depth, and the blood vessel can be better imaged.
At present, the examination technologies for cerebrovascular diseases include Magnetic Resonance Angiography (MRA), CT angiography (CTA) and Digital Subtraction Angiography (DSA), but the resolutions are relatively low, wherein the resolution of MRA is in millimeter level, and the resolution of DSA is in sub-millimeter level; furthermore, MRA, CTA and DSA require the injection of contrast agents, which are also widely used in vascular imaging techniques, but there is still a big debate about the safety of contrast agents, which are harmful to human organs and even risk of death.
Therefore, it is important to provide a means for cerebrovascular examination with higher resolution and without the need for a contrast medium to detect cerebrovascular diseases.
Disclosure of Invention
In order to solve the above problems, the present invention provides a cerebrovascular imaging apparatus based on swept-frequency adaptive optical OCT, so as to solve one or more technical problems in the prior art, and to provide at least one of the advantages.
In order to achieve the above object, an embodiment of the present invention provides a cerebrovascular imaging apparatus based on swept-frequency adaptive optics OCT, including: the device comprises a sweep frequency light source, an optical fiber coupler, a reference arm, a sample arm, a detector and a control processor;
one end of the optical fiber coupler is respectively connected with the sweep frequency light source and the detector; the other end of the optical fiber coupler is respectively connected with the reference arm and the sample arm; the other end of the sample arm is over against a sample to be detected; the control processor is respectively connected with the detector and the sample arm;
the swept-frequency light source is used for providing initial light;
the fiber coupler is used for dividing the initial light emitted by the sweep frequency light source into two paths, and the two paths of initial light respectively enter the reference arm and the sample arm;
the reference arm is used for collimating and reflecting an incoming light beam to obtain reference light, and the reference light returns to the optical fiber coupler along the original path;
the sample arm comprises a second collimating mirror, a plurality of 4F systems, a first scanning galvanometer, a second scanning galvanometer, a deformable mirror, a second plane mirror, a focusing lens, a spectroscope and a wavefront sensor;
the light beam entering the sample arm is collimated by the second collimating mirror, then passes through the spectroscope, enters a 4F system, reaches the first scanning galvanometer, then passes through a 4F system, reaches the second scanning galvanometer, then passes through a 4F system, enters the deformable mirror, then passes through a 4F system, reaches the second plane mirror, and finally is focused to a sample to be measured through the focusing lens;
the sample light reflected by the surface of the sample to be detected returns through the original path and is divided into two beams when reaching the spectroscope, one beam enters the wavefront sensor after being reflected by the spectroscope, the other beam returns to the optical fiber coupler through the spectroscope, and the sample light entering the optical fiber coupler interferes with the reference light to generate an interference signal.
The detector is used for acquiring the interference signal and transmitting the interference signal to the control processor;
and the control processor is used for processing and operating the received interference signals to generate the cerebrovascular image.
Further, the detector is a balanced detector.
Further, the optical fiber coupler comprises a first coupler, a second coupler and a third coupler;
the first coupler, the second coupler and the third coupler are all 2 × 2 optical fiber couplers;
one input end of the first coupler is connected with the swept-frequency light source, the other input end of the first coupler is connected with the balance detector, one output end of the first coupler is emptied, and the other output end of the first coupler is connected with one input end of the second coupler;
one input end of the third coupler is connected with the balance detector, and the other input end of the third coupler is empty; one output end of the third coupler is connected with the other input end of the second coupler, and the other output end of the third coupler is emptied;
and one output end of the second coupler is connected with the reference arm, and the other output end of the second coupler is connected with the sample arm.
Furthermore, the reference arm comprises a first collimating mirror and a first plane mirror, a light beam entering the reference arm reaches the first plane mirror after being collimated by the first collimating mirror, and is reflected by the first plane mirror to obtain reference light, and the reference light returns to the optical fiber coupler along the original path.
Further, the 4F system consists of two toroidal mirrors.
Further, the deformable mirror is an electrostatically actuated MEMS deformable mirror.
Further, the wavefront sensor includes a 132 × 132 microlens array and an area-array camera.
Further, the control processor comprises a first control processor and a second control processor, the first control processor is electrically connected with the wavefront sensor and the deformable mirror respectively, and the second control processor is electrically connected with the first scanning galvanometer, the second scanning galvanometer and the detector respectively.
Furthermore, the center wavelength of the swept-frequency light source is 1040-1310nm, the scanning speed is 50-100KHZ, and the coherence length is 10-15 mm.
The invention has the beneficial effects that: the invention discloses a cerebrovascular imaging device based on sweep-frequency adaptive optical OCT, which comprises a sweep-frequency light source, an optical fiber coupler, a reference arm, a sample arm, a detector and a control processor. The sweep frequency light source is adopted, so that the test sensitivity is improved, and the depth information of the system can be better detected; the cerebrovascular imaging device does not need contrast medium, so that the injury to a human body is avoided.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings needed to be used in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art to obtain other drawings without inventive exercise.
FIG. 1 is a schematic structural diagram of a cerebrovascular imaging apparatus based on swept-frequency adaptive optics OCT according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of the structure of a wavefront sensor in an embodiment of the present invention;
fig. 3 is a schematic structural diagram of an area-array camera according to an embodiment of the invention.
Detailed Description
The conception, specific structure and technical effects of the present disclosure will be described clearly and completely with reference to the accompanying drawings and embodiments, so that the purpose, scheme and effects of the present disclosure can be fully understood. It should be noted that the embodiments and features of the embodiments in the present application may be combined with each other without conflict.
Referring to fig. 1, a cerebrovascular imaging apparatus based on swept-frequency adaptive optical OCT according to an embodiment of the present invention includes a swept-frequency light source 1, a fiber coupler, a reference arm, a sample arm, a detector 25, and a control processor;
one end of the optical fiber coupler is respectively connected with the sweep frequency light source 1 and the detector 25; the other end of the optical fiber coupler is respectively connected with the reference arm and the sample arm; the other end of the sample arm is over against a sample to be detected; the control processor is connected to the detector 25 and the sample arm, respectively;
the swept-frequency light source 1 is used for providing initial light;
the optical fiber coupler is used for dividing the initial light emitted by the sweep frequency light source 1 into two paths, and the two paths of initial light respectively enter the reference arm and the sample arm;
the reference arm is used for collimating and reflecting an incoming light beam to obtain reference light, and the reference light returns to the optical fiber coupler along the original path;
the sample arm comprises a second collimating mirror 7, a spectroscope 8, a wavefront sensor 9, a first toroidal mirror 10, a second toroidal mirror 11, a first scanning galvanometer 12, a third toroidal mirror 13, a fourth toroidal mirror 14, a second scanning galvanometer 15, a fifth toroidal mirror 16, a sixth toroidal mirror 17, a deformable mirror 18, a seventh toroidal mirror 19, an eighth toroidal mirror 20, a second flat mirror 21 and a focusing lens 22; the first and second toroidal mirrors 10 and 11, the third and fourth toroidal mirrors 13 and 14, the fifth and sixth toroidal mirrors 16 and 17, and the seventh and eighth toroidal mirrors 19 and 20 respectively form 4F systems.
The light beam entering the sample arm is collimated by the second collimating lens 7, passes through the beam splitter 8, enters a 4F system, reaches the first scanning galvanometer 12, then passes through a 4F system, reaches the second scanning galvanometer 15, passes through a 4F system, enters the deformable mirror 18, then passes through a 4F system, reaches the second plane mirror 21, and finally is focused to the sample to be measured by the focusing lens 22.
The sample light reflected by the surface of the sample to be detected returns through the original path and is divided into two beams when reaching the spectroscope 8, one beam is reflected by the spectroscope 8 and enters the wavefront sensor 9, the other beam passes through the spectroscope 8 and returns to the optical fiber coupler, and the sample light entering the optical fiber coupler interferes with the reference light to generate an interference signal.
The detector 25 is used for acquiring the interference signal and transmitting the interference signal to the control processor;
and the control processor is used for processing and operating the received interference signals to generate the cerebrovascular image.
As a further improvement of the technical scheme, the detector 25 is a balanced detector, the optical fiber coupler comprises a first coupler 2, a second coupler 3 and a third coupler 4, the first coupler 2, the second coupler 3 and the third coupler 4 are all 2 × 2 optical fiber couplers, one input end of the first coupler 2 is connected with the swept-frequency light source 1, the other input end of the first coupler 2 is connected with the detector 25, one output end of the first coupler 2 is empty, the other output end of the first coupler is connected with one input end of the second coupler 3, one input end of the third coupler 4 is connected with the detector 25, the other input end of the third coupler 4 is empty, one output end of the third coupler 4 is connected with the other input end of the second coupler 3, the other output end of the third coupler 4 is empty, one output end of the second coupler 3 is connected with the reference arm, and the other output end of the second coupler 3 is connected with the sample arm;
as a further improvement of the above technical solution, the reference arm includes a first collimating mirror 5 and a first plane mirror 6, a light beam entering the reference arm reaches the first plane mirror 6 after being collimated by the first collimating mirror 5, and is reflected by the first plane mirror 6 to obtain reference light, and the reference light returns to the optical fiber coupler along the original path;
as a further improvement of the above technical solution, the control processor includes a first control processor 23 and a second control processor 24, the first control processor 23 is electrically connected to the wavefront sensor 9 and the deformable mirror 18, respectively, and the second control processor 24 is electrically connected to the first scanning mirror 12, the second scanning mirror 15, and the detector 25, respectively.
When the cerebrovascular imaging device provided by this embodiment works, the initial light emitted by the sweep light source 1 enters the first coupler 2 of 2 × 2, and is divided into two beams of light, one beam is emptied, the other beam enters the second coupler 3, the light entering the second coupler 3 is divided into two beams, one beam enters the reference arm, is collimated by the first collimating mirror 5 and then hits the first plane mirror 6 to be reflected to obtain the reference light, the reference light returns to the fiber coupler along the original path, the other beam enters the sample arm, is collimated by the second collimating mirror 7 and then passes through the beam splitter 8, then enters the 4F system composed of the first annular mirror 10 and the second annular mirror 11 to reach the first scanning mirror 12, and then enters the second scanning galvanometer 15 through the 4F system composed of the third annular mirror 13 and the fourth annular mirror 14, then passes through the 4F system composed of the fifth annular mirror 16 and the sixth annular mirror 17 to enter the deformable mirror 18, and finally passes through the 4F system composed of the seventh annular mirror 19 and the eighth annular mirror 20 to become a beam of parallel cerebrovascular light, and passes through the focusing lens 21 and is detected by the focusing lens 22;
the light is reflected on the cerebrovascular tissue to obtain sample light, the sample light returns along the original path, when reaching the spectroscope 8, a part of the sample light is reflected by the spectroscope 8 to enter the wavefront sensor 9 to obtain a wavefront phase difference, and then the wavefront phase difference is transmitted to the first control processor 23, and the first control processor 23 adjusts the deformable mirror 18 through calculation so as to achieve the purpose of correcting the wavefront phase difference; the other part of light passes through the spectroscope 8 and enters the second coupler 3, the sample light entering the second coupler 3 interferes with the reference light to generate an interference signal, the interference signal is equally divided into two light rays, and then the two light rays pass through the first coupler 2 and the third coupler 4 respectively and enter the detector 25. The interference signal received by the detector 25 is transmitted to the second control processor 24 through analog-to-digital conversion, and the second control processor 24 performs data processing according to the information transmitted by the detector 25 to obtain the cerebrovascular chart.
The deformable mirror 18 is one of important parts in the adaptive optical system, compensates wavefront phase distortion by changing the surface shape thereof, and corrects wavefront errors as a wavefront correction device, so that the deformable mirror 18 is related to the correction capability and correction accuracy of the whole adaptive optical system, and in the prior art, the surface shape is changed by piezoelectric control; also, in a preferred embodiment of the present invention, the deformable mirror 18 is a MEMS deformable mirror manufactured by Boston Micromachining Corporation (BMC), which uses electrostatic actuation, does not generate hysteresis like a piezoelectric deformable mirror when deformed, and can rapidly change the wavefront phase, thereby greatly improving the working performance of the system.
Referring to fig. 2 and 3, the wavefront sensor 9 provided in the embodiment of the present invention is also one of the important components in the adaptive optics system, which is generally a hartmann-shack wavefront sensor, and the sensor is generally composed of a set of microlens arrays 901 and an area array camera 902, and the specific working principle is that the microlens arrays with the same aperture size and focal length divide the main aperture into a plurality of sub apertures for imaging respectively, the area array camera measures the image point of each sub aperture, calculates the spot centroid of each image point according to the position and light intensity distribution of the image point spot, and obtains the wavefront average slope in the sub aperture range of the distorted wavefront divided by the microlens arrays by the geometric relationship by comparing with the standard ideal point position, thereby obtaining the wavefront phase distribution over the whole aperture.
The swept-frequency light source 1 is a main factor influencing the resolution of the device, and the ideal swept-frequency light source 1 needs to satisfy linear frequency scanning, narrow instantaneous line width, wide swept-frequency range and high output power, so preferably, the center wavelength of the swept-frequency light source 1 of the embodiment of the present invention is 1040 1310nm, the scanning rate is 50-100KHZ, and the coherence length is 10-15 mm; in a preferred embodiment, the central wavelength of the swept-source 1 is 1040nm, the scanning rate is 100KHZ, and the coherence length is 12mm, such as OCT1060 from AXSUN; in another embodiment, the swept source 1 has a center wavelength of 1200nm, a sweep rate of 70KHZ, and a coherence length of 15 mm.
According to the embodiment of the invention, the self-adaptive optical elements such as the wavefront sensor 9 and the deformable mirror 18 are introduced into the sample light path, the wavefront phase difference is captured, and then the deformable mirror 18 is adjusted through the control processor, so that the system resolution can be greatly improved. Furthermore, the swept-frequency light source 1 is adopted, and the parameter optimization selection is carried out, so that the test sensitivity is improved, and the depth information of the system can be better detected. Moreover, the cerebrovascular imaging device based on the sweep frequency adaptive optics OCT does not need contrast medium, completely detects without wound, and avoids damage and potential risk to human bodies.
Meanwhile, the cerebrovascular imaging device based on the sweep frequency adaptive optics OCT has reasonable light path design and compact structure.
Variations and modifications to the above-described embodiments may occur to those skilled in the art, which fall within the scope and spirit of the above description. Therefore, the present invention is not limited to the specific embodiments disclosed and described above, and some modifications and variations of the present invention should fall within the scope of the claims of the present invention. Furthermore, although specific terms are employed herein, they are used in a generic and descriptive sense only and not for purposes of limitation.
Claims (9)
1. A swept-frequency adaptive Optics (OCT) -based cerebrovascular imaging apparatus, comprising: the device comprises a sweep frequency light source, an optical fiber coupler, a reference arm, a sample arm, a detector and a control processor;
one end of the optical fiber coupler is respectively connected with the sweep frequency light source and the detector; the other end of the optical fiber coupler is respectively connected with the reference arm and the sample arm; the other end of the sample arm is over against a sample to be detected; the control processor is respectively connected with the detector and the sample arm;
the swept-frequency light source is used for providing initial light;
the fiber coupler is used for dividing the initial light emitted by the sweep frequency light source into two paths, and the two paths of initial light respectively enter the reference arm and the sample arm;
the reference arm is used for collimating and reflecting an incoming light beam to obtain reference light, and the reference light returns to the optical fiber coupler along the original path;
the sample arm comprises a second collimating mirror, a plurality of 4F systems, a first scanning galvanometer, a second scanning galvanometer, a deformable mirror, a second plane mirror, a focusing lens, a spectroscope and a wavefront sensor;
the light beam entering the sample arm is collimated by the second collimating mirror, then passes through the spectroscope, enters a 4F system, reaches the first scanning galvanometer, then passes through a 4F system, reaches the second scanning galvanometer, then passes through a 4F system, enters the deformable mirror, then passes through a 4F system, reaches the second plane mirror, and finally is focused to a sample to be measured through the focusing lens;
the sample light reflected by the surface of the sample to be detected returns through the original path and is divided into two beams when reaching the spectroscope, one beam enters the wavefront sensor after being reflected by the spectroscope, the other beam returns to the optical fiber coupler through the spectroscope, and the sample light entering the optical fiber coupler interferes with the reference light to generate an interference signal;
the detector is used for acquiring the interference signal and transmitting the interference signal to the control processor;
and the control processor is used for processing and operating the received interference signals to generate the cerebrovascular image.
2. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, characterized in that the detector is a balanced detector.
3. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 2, characterized in that the fiber coupler comprises a first coupler, a second coupler and a third coupler;
the first coupler, the second coupler and the third coupler are all 2 × 2 optical fiber couplers;
one input end of the first coupler is connected with the swept-frequency light source, the other input end of the first coupler is connected with the balance detector, one output end of the first coupler is emptied, and the other output end of the first coupler is connected with one input end of the second coupler;
one input end of the third coupler is connected with the balance detector, and the other input end of the third coupler is empty; one output end of the third coupler is connected with the other input end of the second coupler, and the other output end of the third coupler is emptied;
and one output end of the second coupler is connected with the reference arm, and the other output end of the second coupler is connected with the sample arm.
4. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, wherein the reference arm comprises a first collimating mirror and a first plane mirror, a light beam entering the reference arm reaches the first plane mirror after being collimated by the first collimating mirror, and is reflected by the first plane mirror 6 to obtain a reference light, and the reference light returns to the fiber coupler along the original path.
5. A swept-frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, wherein the 4F system consists of two toroidal mirrors.
6. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, characterized in that the deformable mirror is an electrostatically driven MEMS deformable mirror.
7. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, wherein the wavefront sensor comprises a 132 × 132 microlens array and an area-array camera.
8. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, wherein the control processor comprises a first control processor and a second control processor, the first control processor being electrically connected to the wavefront sensor and deformable mirror, respectively, and the second control processor being electrically connected to the first galvanometer mirror, second galvanometer mirror, and detector, respectively.
9. A swept frequency adaptive optics OCT-based cerebrovascular imaging apparatus according to claim 1, wherein the swept frequency light source has a center wavelength of 1040-1310nm, a scan rate of 50-100KHZ and a coherence length of 10-15 mm.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010303433.XA CN111436907A (en) | 2020-04-17 | 2020-04-17 | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010303433.XA CN111436907A (en) | 2020-04-17 | 2020-04-17 | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN111436907A true CN111436907A (en) | 2020-07-24 |
Family
ID=71655963
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202010303433.XA Pending CN111436907A (en) | 2020-04-17 | 2020-04-17 | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN111436907A (en) |
Citations (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103070665A (en) * | 2012-10-12 | 2013-05-01 | 中国科学院光电技术研究所 | Self-adaptive frequency-sweeping optical coherence tomography system based on double wave front corrector |
| CA2887052A1 (en) * | 2012-10-12 | 2014-04-17 | Thorlabs, Inc. | Compact, low dispersion, and low aberration adaptive optics scanning system |
| CN103799975A (en) * | 2014-02-26 | 2014-05-21 | 中国科学院光电技术研究所 | Adaptive optics OCT retinal imager employing coherence gate wavefront sensor |
| CN106308744A (en) * | 2015-06-15 | 2017-01-11 | 南京理工大学 | Handheld human body any surface position skin frequency sweeping optical coherence tomography imaging apparatus |
| CN108061968A (en) * | 2018-01-05 | 2018-05-22 | 京东方科技集团股份有限公司 | A kind of head-up display device and display image correcting method |
| CN108523852A (en) * | 2018-05-10 | 2018-09-14 | 视微影像(河南)科技有限公司 | A kind of optical interference imaging system of frequency sweep OCT |
| CN109691971A (en) * | 2018-12-29 | 2019-04-30 | 佛山科学技术学院 | The optical coherence tomography system of anterior ocular segment tissue dynamic parameter fast imaging |
| CN109700436A (en) * | 2019-01-28 | 2019-05-03 | 广东唯仁医疗科技有限公司 | A kind of Dermal microvessel form and blood flow detection device |
| CN109965842A (en) * | 2019-04-23 | 2019-07-05 | 广东唯仁医疗科技有限公司 | Convenient for distinguishing the AO-OCT imaging device of sugar net disease and MacTel disease |
| CN110074752A (en) * | 2019-04-23 | 2019-08-02 | 广东唯仁医疗科技有限公司 | A kind of cone cell imaging device |
| CN110793941A (en) * | 2019-10-10 | 2020-02-14 | 成都贝瑞光电科技股份有限公司 | System for intelligent resolution laser optical tomography method |
| CN210130817U (en) * | 2019-01-28 | 2020-03-10 | 广东唯仁医疗科技有限公司 | Tumor microvascular imaging device based on SS-OCT |
| CN210249850U (en) * | 2018-12-29 | 2020-04-07 | 佛山科学技术学院 | Blood oxygen measuring device for human eye capillary |
| CN212326378U (en) * | 2020-04-17 | 2021-01-12 | 佛山科学技术学院 | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT |
-
2020
- 2020-04-17 CN CN202010303433.XA patent/CN111436907A/en active Pending
Patent Citations (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103070665A (en) * | 2012-10-12 | 2013-05-01 | 中国科学院光电技术研究所 | Self-adaptive frequency-sweeping optical coherence tomography system based on double wave front corrector |
| CA2887052A1 (en) * | 2012-10-12 | 2014-04-17 | Thorlabs, Inc. | Compact, low dispersion, and low aberration adaptive optics scanning system |
| CN103799975A (en) * | 2014-02-26 | 2014-05-21 | 中国科学院光电技术研究所 | Adaptive optics OCT retinal imager employing coherence gate wavefront sensor |
| CN106308744A (en) * | 2015-06-15 | 2017-01-11 | 南京理工大学 | Handheld human body any surface position skin frequency sweeping optical coherence tomography imaging apparatus |
| CN108061968A (en) * | 2018-01-05 | 2018-05-22 | 京东方科技集团股份有限公司 | A kind of head-up display device and display image correcting method |
| CN108523852A (en) * | 2018-05-10 | 2018-09-14 | 视微影像(河南)科技有限公司 | A kind of optical interference imaging system of frequency sweep OCT |
| CN109691971A (en) * | 2018-12-29 | 2019-04-30 | 佛山科学技术学院 | The optical coherence tomography system of anterior ocular segment tissue dynamic parameter fast imaging |
| CN210249850U (en) * | 2018-12-29 | 2020-04-07 | 佛山科学技术学院 | Blood oxygen measuring device for human eye capillary |
| CN109700436A (en) * | 2019-01-28 | 2019-05-03 | 广东唯仁医疗科技有限公司 | A kind of Dermal microvessel form and blood flow detection device |
| CN210130817U (en) * | 2019-01-28 | 2020-03-10 | 广东唯仁医疗科技有限公司 | Tumor microvascular imaging device based on SS-OCT |
| CN109965842A (en) * | 2019-04-23 | 2019-07-05 | 广东唯仁医疗科技有限公司 | Convenient for distinguishing the AO-OCT imaging device of sugar net disease and MacTel disease |
| CN110074752A (en) * | 2019-04-23 | 2019-08-02 | 广东唯仁医疗科技有限公司 | A kind of cone cell imaging device |
| CN110793941A (en) * | 2019-10-10 | 2020-02-14 | 成都贝瑞光电科技股份有限公司 | System for intelligent resolution laser optical tomography method |
| CN212326378U (en) * | 2020-04-17 | 2021-01-12 | 佛山科学技术学院 | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT |
Non-Patent Citations (2)
| Title |
|---|
| HUANG, YP (HUANG, YANPING) [1] ; ZHANG, QQ (ZHANG, QINQIN) [1] ; THORELL, MR (THORELL, MARIANA R.) [2] ;: "Swept-Source OCT Angiography of the Retinal Vasculature Using Intensity Differentiation-based Optical Microangiography Algorithms", 《OPHTHALMIC SURGERY LASERS & IMAGING RETINA 》, vol. 45, no. 5, pages 382 - 389 * |
| KUEHLEWEIN, L (KUEHLEWEIN, LAURA) [1] , [2] ; AN, L (AN, LIN) [3] ; DURBIN, MK (DURBIN, MARY K.) [3] ; SADDA, SR (SADDA, SRINIVAS : "Imaging Areas of Retinal Nonperfusion in Ischemic Branch Retinal Vein Occlusion With Swept-Source OCT Microangiography", 《OPHTHALMIC SURGERY LASERS & IMAGING RETINA 》, vol. 46, no. 2, pages 249 - 252 * |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JP6768747B2 (en) | Two-dimensional confocal imaging using OCT light source and scanning optics | |
| JP5591235B2 (en) | Extended range imaging | |
| EP0956810B1 (en) | Simultaneously measuring the length and refractive error of an eye | |
| US8472028B2 (en) | Optical coherence tomographic apparatus | |
| US20120133888A1 (en) | scanning ophthalmoscopes | |
| CN110035689A (en) | System and method for wide visual field optical coherence tomography | |
| CN102970919A (en) | Optical coherence tomography and method thereof | |
| CN110013212B (en) | Multi-parameter and multi-functional eye measuring instrument based on optical coherence tomography | |
| JP7175982B2 (en) | Optical measurement device and sample observation method | |
| US20120013909A1 (en) | Apparatus and method of monitoring and measurement using spectral low coherence interferometry | |
| US11154192B2 (en) | Method and arrangement for high-resolution topography of the cornea of an eye | |
| EP3637041B1 (en) | Light interference unit and light interference measurement device | |
| CN212326378U (en) | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT | |
| CN109700426B (en) | Portable AO-OCT imaging device | |
| CN210130811U (en) | Multi-parameter and multi-functional eye measuring instrument based on optical coherence tomography | |
| CN109691975B (en) | Device and method for measuring cornea curvature of eye based on SD-OCT | |
| CN111436907A (en) | Cerebrovascular imaging device based on sweep frequency adaptive optics OCT | |
| JP6917663B2 (en) | Optical interference unit for optical coherence tomography equipment | |
| CN209915944U (en) | Portable AO-OCT imaging device | |
| CN210130810U (en) | Device for tracking eyeball movement based on optical dry method | |
| US20240241041A1 (en) | Optical measurement apparatus and method of rapid measurement | |
| KR102178998B1 (en) | Apparatus of optical coherence tomography of optical path length encoding dual-beam scanning for wide range of the retinal blood velocity measurements and method thereof | |
| CN117503047B (en) | Large target surface zoom OCT system and application thereof in fundus and anterior ocular segment detection | |
| CN115634098B (en) | High-speed ophthalmic surgery navigation OCT system and implementation method | |
| CN110477849B (en) | Self-calibration optical coherent scanner and sampling method |
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 | ||
| CB02 | Change of applicant information | ||
| CB02 | Change of applicant information |
Country or region after: China Address after: No.33 Guangyun Road, Shishan town, Nanhai District, Foshan City, Guangdong Province Applicant after: Foshan University Address before: No.33 Guangyun Road, Shishan town, Nanhai District, Foshan City, Guangdong Province Applicant before: FOSHAN University Country or region before: China |
|
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20200724 |