CN103211567A - Integrated super-miniature optical coherence tomography probe - Google Patents
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Abstract
The invention relates to the technical field of medical apparatus and instruments and provides an integrated super-miniature optical coherence tomography probe. The probe comprises a hot expanded core optical fiber, wherein the hot expanded core optical fiber comprises a single mode optical fiber part, a hot expanded core part and an inclined reflection part; the hot expanded core part is located at one end of the single mode optical fiber part; and the inclined reflection part is an inclined reflection face polished on the other end of the hot expanded core part. The integrated super-miniature optical coherence tomography probe disclosed by the invention adopts a method of completely eliminating the two reflection faces, so that a reflected light interference phenomenon does not happen.
Description
[
Technical field]
The present invention relates to technical field of medical instruments, particularly a kind of detection that is applied to cardiovascular OCT or tissue narrow space is to prevent the integrated superminiature optical coherence tomography probe of interference ring.
[
Background technology]
Along with the reach of science, in medical science with in biology, various Image-forming instruments have successively appearred, for example: ultra sonic imaging, X-ray imaging, CT, MRT and PET or the like, but what all have oneself advantage and weak point with these instruments.Ultra sonic imaging depends on the acoustic impedance of biological tissue, and poor contrast is difficult to find early stage canceration; The X-ray imaging depends on the density of biological tissue, density is big more, image is just white more, but then can't not differentiate because of contrast is high for the approaching Different Organs of density and the image of tissue, and radioscopy makes tissue suffer the effect of strong ionizing radiation, and incident high-energy can make biological tissue's ionization.In addition, the CT in the chromatography imaging technique, MRT and PET equipment and cost of use costliness have certain damaging action to human body; For example: X-CT has higher imaging depth, can survey whole health, resolution can reach 0.7mm to 2.0mm, the image reconstruction work of not overscanning and intensive all will spend the long time, obtaining a complete CT image generally needed for tens seconds, so it is not suitable for doing real-time high-resolution imaging; MRI causes atomic resonance in the body to send their information itself based on high-intensity magnetic field and high-frequency signal, and its resolution is also relatively low.And optical image technology becomes relatively ideal technology, and wherein topmost representative is optical coherence tomography technology (optical coherence tomography) OCT.Its advantage is: utilize infrared light to the human zero damage as light source (generally being 830nm or 1310nm), utilize the principle of door coherence time to realize chromatography, have very high resolution (micron order), can realize noncontact, radiationless, high-resolution and realtime imaging and in the body biopsy.It is owing to possess above-mentioned special advantage, and the optical coherence tomography technology is a kind of medical imaging technology with fastest developing speed over nearly 20 years, is mainly used in ophthalmology, skin, dentistry, cardiovascular, respiratory tract and gastrointestinal tract, early-stage cancer detection etc.
The core of OCT technology is a Michelson's interferometer, because the OCT technology derives from white light interferometric method, optical coherence domain reflectometry measurement technology in fact the earliest.The coherent light that this technology uses a wideband light source to send carries out the measurement of reflected field, and has obtained the axial resolution of 10um by experiment and greater than the dynamic range of 100dB.And traditional image method mainly comprises nuclear magnetic resonance (NMR) vessel imaging and angiographic imaging, yet these imagings are merely able to present the profile or the in-profile of blood vessel, detail section to blood vessel wall and lumen of vessels manifests very fuzzy, comprise the size, composition, crackle of blood vessel wall tremulous pulse dissipating rashes piece etc., these information have important clinic value for vascular integrity assessment and prediction.And, because X ray has very strong radioactivity, so also limited usability to a certain extent.Therefore, ideal blood vessel imaging technology should not only can find the focus zone of blood vessel but also can analyze this regional lesion properties guaranteeing under the prerequisite of necessary security, thereby provides effective scientific basis for clinical diagnosis.(intravascular ultrasound tomography IVUS) can directly stretch into the profile scanning imaging that internal blood vessel is carried out blood vessel with a miniature ultrasound imaging probe to intravascular ultrasound imaging.This technology has improved the resolution of blood vessel imaging to a certain extent, can find some tangible focus zone, but because the frequency of the ultrasonic probe that adopts is generally between 20-50MHz, correspondence image resolution is approximately about 200-100 μ m, this resolution also is not enough to see clearly the details of blood vessel wall, has many limitation.And optical coherence tomography chromatography (the optical coherence tomography that adopts developed recently to get up, OCT) technology can realize the high-resolution imaging of micron order in the cardiovascular, and the effect of clinical discriminating and diagnosis coronary atherosclerosis and therapeutic intervention is carried out tracking evaluation.
The appearance of endoscopic OCT is in the future carrying out the in-vivo tissue pathological changes and cancer diagnosis provides strong help.OCT imaging in the blood vessel (Intravascular OCT IV-OCT) has the unique function that can present arteriosclerotic micro details, particularly those be considered to be easy to will unexpected disruptive lump.The sharpest edges of this technology are exactly its high-resolution, exceed 10 times than the resolution of intravascular ultrasound imaging, can observe atheromatous plaque and the coronary artery micro-structure changes from tissue morphology.In addition, be implanted into the observation and the location of support for blood vessel, the OCT imaging is that common shadowgraph technique and intravascular ultrasound imaging are incomparable in the blood vessel.Whether fully the doctor can clearly observe whether adherent fully, expansion, torn tissue, tissue prolapsus and the frame support rails situation such as whether be evenly distributed of support from the result of OCT imaging, and these are extremely important for uses of estimating surgical stent.Present development along with the OCT technology, can realize IC high speed, high resolution imaging, and because the appearance of miniaturization imaging fiber conduit probe can realize the imaging of artery stenosis inside pipe wall, these all are that common imaging technique institute is unapproachable.OCT imaging catheter and intravascular ultrasound catheter compare, and the OCT conduit only is made of an optical fiber, and is without any need for pick off, simple and practical.
The OCT imaging system is just to begin recent years to grow up in the blood vessel, and it mainly combines technology such as optical imagery, mechanical scanning, signal processing, is the product of multidisciplinary cross coupled.Miniature OCT imaging catheter not only is used for tremulous pulse, vein and also can be used for lung airway, can also be used for the micropore of the detection of various narrow spaces such as femto-second laser processing.At the characteristics of cardiovascular imaging, spy upon head in needs are special and solve a following key issue:
1, probe miniaturization issues because cardiovascular OCT probe will enter into the tubulose arteries of human body, is position the narrowest in the human body, requires probe size less than 250um even littler.And traditional endoscopic OCT probe is made up of optical fiber and GRIN Lens and prism, and general GRIN Lens is of a size of 1.8mm, 1mm.The endoscopic OCT probe stock size outside dimension minimum of therefore making is 1mm only, is difficult to produce reach the requirement of cardiovascular OCT probe size.
2, eliminate the difficult problem of interference ring, because endoscopic OCT probe is made up of optical fiber and GRIN Lens and prism, general optical system return loss is about 60dB, but because the signal to noise ratio of OCT system can reach more than the 100dB, therefore the reflected light of each end face generation on light path still can produce the phenomenon of mutual interference, cause the appearance of interference ring, and the very serious quality that has interfered with image of interference ring must thoroughly be eliminated interference ring.
U.S. Pat discloses a kind of mini optical fibre probe for No. 4740047, but because fibre-optical probe increases lens and do not come collimated beam, so can't allow beam convergence, so signal is very weak, can't reach the instructions for use of OCT probe.
Chinese patent CN100407980C number, a kind of scanning micro-optical probe is disclosed, can satisfy the demand of size microminiaturization, but, occur a plurality of reflectings surface in the middle of causing because the microprism that whole optical probe is made by optical fiber, coreless fiber, self-focusing optical fiber, band angle coreless fiber is formed, each reflecting surface all can produce certain reflected light, thereby cause the phenomenon that interference ring occurs, and a plurality of joint face is when connecting, technology is complicated, manufacture difficulty is big, the production cost height.To be exactly a kind of scheme of announcing in the patent be made up of a kind of GRIN Lens and reflecting mirror and optical fiber less than 300um Fig. 1.Two end faces of GRIN Lens all are the planes, and the reflected light of two plane generations can produce interference ring, and concrete interference ring is seen Fig. 2.In the optical coherence tomography system, the reflex strength relation between the reflecting surface on the propagation path of light can be detected.Two reflectings surface produce in very near distance than strong reflection light in Fig. 2, light is multiple reflection in two reflectings surface, the light of multiple reflection will cause the appearance of interference ring (ciomatic flare) through coherent imaging, and why be referred to as ghost is because this interference ring was non-existent originally in image, and this can cause the decline of image quality.Especially when interference ring and actual imaging of tissue are overlapping, can cause and can't differentiate interference ring and real image, this is the difficult problem of a maximum of OCT probe.And, two very adverse factors are arranged owing to adopted the plastic protective sleeve pipe in the patent, and the first, the prismatical refractive index of the refractive index of plastic protective sleeve and glass-reflected does not match, and therefore can cause more reflected light to occur, and might cause interference ring yet.In addition because plastic bushing can only be done circular cross section, therefore collimated beam is equivalent to pass through a cylindrical lens through behind the plastic bushing, can carry out one to light beam and converge effect, and causing the outgoing hot spot is ellipse light spot, produce optical distortion, can influence the image quality of OCT so greatly.
At this, U.S. Pat 7805034 has been introduced the mini optical fibre probe of a kind of elimination ghost (being interference ring), it is in order to solve the problem of interference ring, must eliminate two planes between the probe, therefore, describe a kind of way that adopts the globe lens welding in the patent, replaced two planes of lens and reflecting mirror with two spheres, reduce plane reflection light greatly, therefore can eliminate interference ring (ciomatic flare).But the shortcoming of this patent has been to use a globe lens, is of a size of diameter 500um, can't satisfy the requirement of the lens diameter size of cardiovascular OCT probe requirement less than 250um.In sum, need a kind of detection that is applied to cardiovascular OCT or tissue narrow space of design, to prevent the imaging probe of interference ring.
[summary of the invention]
Can not to satisfy the technical problem of size simultaneously in order overcoming to exist in the prior art, to the invention provides integrated superminiature optical coherence tomography probe less than the interference ring of 250um and the generation of elimination multiple reflection.
The present invention solves the problems of the technologies described above the technical scheme that is adopted:
Integrated superminiature optical coherence tomography probe, described probe comprises hot core expansion optical fiber, described hot core expansion optical fiber comprises single-mode fiber part, hot core expansion part and inclination reflecting part, described hot core expansion portion is positioned at an end of single-mode fiber, the sloping reflector of described inclination reflecting part for wearing at the other end of hot core expansion part.
According to a preferred embodiment of the invention: the diameter of described probe is between the 125-250um.
According to a preferred embodiment of the invention: the expansion bundle spot size of described probe is 20-100um.
According to a preferred embodiment of the invention: the spot size that converges of described probe is 20-100um.
According to a preferred embodiment of the invention: the sloping reflector angle of described probe is 42 °-60 °.
According to a preferred embodiment of the invention: also establish on the sloping reflector of described probe and be coated with the total reflection rete, and described total reflection rete is a metallic diaphragm.
According to a preferred embodiment of the invention: it is the quartz glass protective layer of 250um-500um that the described probe outside also has diameter, and the light output end of described optical coherence tomography probe is the plane.
With respect to prior art, beneficial effect of the present invention is: adopt the method for thoroughly eliminating these two reflectings surface on the one hand, make it can not produce the reflected light interference, can satisfy the advantage of size on the other hand simultaneously less than the interference ring of 250um and the generation of elimination multiple reflection.
[description of drawings]
Fig. 1 is the structural representation of original optics OCT probe;
Fig. 2 has the image of interference ring after for the imaging of optics OCT probe;
Fig. 3 eliminates the image of interference ring after for the imaging of optics OCT probe;
Fig. 4 is the cut-away view of TEC optical fiber;
Fig. 5 is the structural representation that uses the optic probe of TEC optical fiber fabrication among the embodiment one;
The optic probe structural representation of Fig. 6 embodiment two band flat glass pipes.
Description of reference numerals:
1, single-mode fiber, 2, GRIN Lens, 4, reflecting prism, 5, the expansion bundle core diameter of TEC optical fiber; 6, the non-expansion bundle core diameter portion of TEC optical fiber, 7, covering, 10, the single-mode fiber part, 20, the hot core expansion part; 30, converging beam, 40, the inclination reflecting part, 51, the quartz glass protective layer.
[specific embodiment]
The invention will be further described below in conjunction with drawings and embodiments.
Fig. 1 is general cardiovascular OCT probe, the 1st, and single-mode fiber, the 2nd, GRIN Lens, the 4th, reflecting prism, two planes of GRIN Lens 2 are respectively at single-mode fiber 1 and reflecting prism 4 bonding or weldings, and the reflected light that these two planes produce will cause interference ring.Planar reflected light can calculate by following formula:
In the formula:
Be the plane reflection rate, in optical fiber and welding of GRIN Lens end face or abutting edge,
Be 1.4681(fiber core refractive index),
Be the GRIN Lens refractive index,
=1.55.At GRIN Lens and reflecting prism end face abutting edge or weld, make owing to reflecting prism is generally coreless fiber, so refractive index is identical with single-mode fiber
=1.4681.As can be seen from the above equation, two refractive indexs are low more near reflectance more, therefore will be as much as possible with two refractive index match.Therefore two reflecting surface reflective light intensities are suitable substantially.The formula that calculates return loss is as follows:
RL
1= 10lgR
01 （2）
By calculating as can be known, the reflection echo loss of two faces is 31dB, therefore, two closely the light of identical reflex strength can form interference, produce interference ring (being ghost).
Address this problem, following three kinds of ways arranged:
1, thoroughly eliminates this two reflectings surface, just can not produce reflected light.
2, do not eliminate under the situation of reflecting surface, increase the joint face angle, reduce intensity of reflected light significantly, make reflected light weak to not producing interference.
When bevel angle is 8 when spending, return loss is greater than 90dB, and when bevel angle is 10 when spending, return loss is greater than 100dB.
3, do not eliminate reflecting surface and do not increase under the situation of reflecting surface angle yet, catoptrical distance is zoomed out, make the interference ring that produces exceed the indication range of image.
Because the imaging depth of OCT image is generally 2-3mm, therefore, so long as radius just can not show greater than the image beyond the 5mm, the diameter formula of interference ring is 2nd+ λ/2, and n is the index of refraction in lens, and d is the spacing of two reflectings surface.The refractive index of lens is 1.55, as long as 2nd just can not demonstrate interference ring greater than 10mm on image.And the image of the imaging of elimination interference ring as shown in Figure 3.
Below promptly at above-mentioned put forward thoroughly eliminating these two reflectings surface, just can not produce catoptrical specific embodiment.
Embodiment one
Consult shown in Figure 5, for embodiment provides integrated superminiature optical coherence tomography probe, comprise hot core expansion optical fiber, and hot core expansion optical fiber comprises single-mode fiber part 10, hot core expansion part 20 and inclination reflecting part 40, and hot core expansion part 20 is positioned at an end of single-mode fiber part 10, also be to make the sloping reflector of inclination reflecting part 40 in the end heating of single-mode fiber part 10 for wearing at the other end of hot core expansion part 20.Wherein, the diameter of whole probe is between the 125-250um, selects 125um in the present embodiment for use; The expansion bundle spot size of probe is 20-100um, selects 30um here for use; The spot size of the converging beam 30 of probe is 20-100um, selects 30um here for use; The sloping reflector angle of probe is 42 °-60 °, selects 50 ° here for use; Also establish on the sloping reflector of probe and be coated with the total reflection rete, and the total reflection rete is a metallic diaphragm; It is the quartz glass protective layer of 250um-500um that the probe outside also has diameter, and the light output end of optical coherence tomography probe is the plane.
Because whole optic probe forms by a TEC optical fiber fabrication, without any reflecting surface, therefore thoroughly eliminated the interference ring that reflecting surface brings.
TEC(Thermally-diffusion Expanded Core Fiber) optical fiber has solved a lot of difficult problems about fiber alignment coupling and Power Processing in the single-mode fiber.Its structure is seen shown in Figure 4, comprises the expansion bundle core diameter 5 of TEC optical fiber, the non-expansion bundle core diameter portion 6 and the covering 7 of TEC optical fiber, and TEC optical fiber is to use heat treated mode to make common SiO
2GeO in the optical fiber
2The contained Ge atom of adulterant spreads, and forms expanded core fiber.Its index distribution changes along the optical fiber axle center, so mode field diameter also changes thereupon.Be equivalent to the end portion of optical fiber has directly been become gradient-index lens.Can replace optical fiber to add the structure of gradient-index lens, directly will export optical alignment or focusing.
And the refractivity of general single mode fiber covering and fibre core is by doped with Ge O in fibre core
2Reach.The refractive index of fiber core is higher than the refractive index of fusion pure silicon in the covering.When the heating general single mode fiber, adulterated Ge in the fibre core
4+Ion will spread in fibre cladding, makes the radial refractive index in cross section of optic fibre upper edge be graded profile, thereby reaches the purpose that enlarges mode field diameter.After the thermal-flame that adopts 1600 °-2000 ° carried out uniform heating to the single-mode fiber in about 4mm scope, the Germanium dopants that makes optical fiber be heated in the part fibre core was diffused in the optical fiber, just can reach the effect that expands bundle.Optical fiber still is step optical fiber in bringing-up section not, and refractive index is a step between fibre core and the covering, has then formed graded index profile in bringing-up section.
Normalized frequency
Can not change in whole heating process, optical field distribution still has only basic mode in this explanation TEC optical fiber, and therefore, light still keeps single mode transport in the TEC optical fiber, and the difference of it and general single mode fiber only is the different of mode field diameter.So still, can represent optical field distribution in the TEC optical fiber with Gauss distribution, describe the emergent light characteristic of TEC optical fiber with the transmission characteristic of Gaussian beam.And the external diameter of optical fiber can not be heated change, makes things convenient for the use of TEC optical fiber.Know the mode field diameter after the normalized frequency of single-mode fiber and the core diameter that needs expansion to restraint just can be calculated the expansion bundle.
The single-mode fiber that uses standard in the present embodiment G.652 (healthy and free from worry SMF-28) calculates and expands Shu Xiaoguo, the G.652 fiber core refractive index of optical fiber
Be 1.468, cladding index
Be 1.4628, core diameter
, therefore, when with
During calculating, refractivity
, numerical aperture NA=0.123.Work as heating-up temperature
The time, the diffusion coefficient of single-mode fiber
, before not carrying out heat expansion bundle, GeO in the fiber core
2Doping content
Along with the passage of time that heat expands bundle, GeO in the single-mode fiber fibre core
2Ge
4+GeO in ion and the covering
2Si
4+Ion has carried out heat exchange, so Ge
4+Ionic doping content caused the refractive index of fibre core also progressively to reduce, and the expansion bundle of single-mode fiber part has progressively become gradient index fibre by step optical fiber along with the time of diffusion progressively reduces.
MFD(mode field diameter) is an important parameter of TEC optical fiber.In the making of TEC optical fiber, the MFD of optical fiber depends on heating-up temperature and time.The value of MFD can increasing and enlarge with the increase of heat time heating time and heating-up temperature.Increase heating-up temperature than the MFD that increases more effective expansion optical fiber heat time heating time.In order not destroy the single mode transport characteristic of optical fiber, the key that adopts the TEC technology is the length of control optical fiber heating.Wherein
The=1.468th, fiber core refractive index,
Be to expand bundle back waist of Gaussian beam speckle radius.30um gauss light beam waist diameter is restrainted in the beam waist diameter expansion of 10um is calculated,
=1550nm is a wavelength, and TEC optical fiber is restrainted 30um from common single mode to expansion length is 1.64mm.Usually heated length is 4mm when producing TEC optical fiber.
Embodiment two
Superminiature optical coherence tomography probe in the foregoing description one all can increase quartz glass protecting tube 51 outside, and its structural representation as shown in Figure 6.
With respect to prior art, beneficial effect of the present invention is: adopt the method for thoroughly eliminating these two reflectings surface on the one hand, make it can not produce the reflected light interference, can satisfy the advantage of size on the other hand simultaneously less than the interference ring of 250um and the generation of elimination multiple reflection.
Foregoing detailed description only is exemplary description, and those skilled in the art are under the situation of the scope and spirit that do not break away from the present invention and protected, and the various embodiments according to different actual needs is designed all should belong to protection scope of the present invention.
Claims (7)
1. an integrated superminiature optical coherence tomography is popped one's head in, it is characterized in that: described probe comprises hot core expansion optical fiber, described hot core expansion optical fiber comprises single-mode fiber part (10), hot core expansion part (20) and inclination reflecting part (40), described hot core expansion part (20) is positioned at an end of single-mode fiber part (10), the sloping reflector of described inclination reflecting part (40) for wearing at the other end of hot core expansion part (20).
2. superminiature optical coherence tomography probe according to claim 1, it is characterized in that: the diameter of described probe is between the 125-250um.
3. superminiature optical coherence tomography probe according to claim 1, it is characterized in that: the expansion bundle spot size of described probe is 20-100um.
4. superminiature optical coherence tomography probe according to claim 1, it is characterized in that: the spot size that converges of described probe is 20-100um.
5. superminiature optical coherence tomography probe according to claim 1, it is characterized in that: the sloping reflector angle of described probe is 42 °-60 °.
6. superminiature optical coherence tomography probe according to claim 1 is characterized in that: also establish on the sloping reflector of described probe and be coated with the total reflection rete, and described total reflection rete is a metallic diaphragm.
7. superminiature optical coherence tomography probe according to claim 1 is characterized in that: it is the quartz glass protective layer of 250um-500um that the described probe outside also has diameter, and the light output end of described optical coherence tomography probe is the plane.
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104932087A (en) * | 2015-05-15 | 2015-09-23 | 奥普多威（开曼）控股有限公司 | Integrated optical coherent detection probe |
| CN106913309A (en) * | 2015-07-31 | 2017-07-04 | 浙江大学 | All -fiber endoscopic OCT probe based on unit wimble structure |
| CN108324249A (en) * | 2018-02-07 | 2018-07-27 | 华南师范大学 | Optical coupled and photo-acoustic excitation intravascular photoacoustic imaging probe is realized based on conical fiber simultaneously |
| CN109938679A (en) * | 2019-03-29 | 2019-06-28 | 杭州好克光电仪器有限公司 | Endoscope with protecting pipe |
| CN112842270A (en) * | 2021-01-06 | 2021-05-28 | 浙江大学 | Focal depth expansion probe based on high-order mode energy regulation |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1684624A (en) * | 2002-07-25 | 2005-10-19 | 莱特莱图像公司 | Scanning miniature optical probes with optical distortion correction and rotational control |
| US20070188855A1 (en) * | 2006-01-19 | 2007-08-16 | The General Hospital Corporation | Apparatus for obtaining information for a structure using spectrally-encoded endoscopy teachniques and methods for producing one or more optical arrangements |
| US20090323076A1 (en) * | 2007-05-03 | 2009-12-31 | University Of Washington | High resolution optical coherence tomography based imaging for intraluminal and interstitial use implemented with a reduced form factor |
| CN101711666A (en) * | 2009-11-19 | 2010-05-26 | 浙江大学 | Two-dimensional scan fiber optic probe for endoscopic optical coherence tomography |
| CN101912254A (en) * | 2010-07-27 | 2010-12-15 | 东南大学 | Fiber-optics probe of common-path optical-coherence tomography system |
| CN102436030A (en) * | 2010-09-29 | 2012-05-02 | 日立电线株式会社 | Optical fiber end processing method and optical fiber end processing apparatus |
| CN203263350U (en) * | 2013-05-07 | 2013-11-06 | 深圳市中科微光医疗器械技术有限公司 | Integrated ultra-micro optical coherence tomography probe |
-
2013
- 2013-05-07 CN CN201310164258.0A patent/CN103211567B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1684624A (en) * | 2002-07-25 | 2005-10-19 | 莱特莱图像公司 | Scanning miniature optical probes with optical distortion correction and rotational control |
| US20070188855A1 (en) * | 2006-01-19 | 2007-08-16 | The General Hospital Corporation | Apparatus for obtaining information for a structure using spectrally-encoded endoscopy teachniques and methods for producing one or more optical arrangements |
| US20090323076A1 (en) * | 2007-05-03 | 2009-12-31 | University Of Washington | High resolution optical coherence tomography based imaging for intraluminal and interstitial use implemented with a reduced form factor |
| CN101711666A (en) * | 2009-11-19 | 2010-05-26 | 浙江大学 | Two-dimensional scan fiber optic probe for endoscopic optical coherence tomography |
| CN101912254A (en) * | 2010-07-27 | 2010-12-15 | 东南大学 | Fiber-optics probe of common-path optical-coherence tomography system |
| CN102436030A (en) * | 2010-09-29 | 2012-05-02 | 日立电线株式会社 | Optical fiber end processing method and optical fiber end processing apparatus |
| CN203263350U (en) * | 2013-05-07 | 2013-11-06 | 深圳市中科微光医疗器械技术有限公司 | Integrated ultra-micro optical coherence tomography probe |
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104932087A (en) * | 2015-05-15 | 2015-09-23 | 奥普多威（开曼）控股有限公司 | Integrated optical coherent detection probe |
| CN106913309A (en) * | 2015-07-31 | 2017-07-04 | 浙江大学 | All -fiber endoscopic OCT probe based on unit wimble structure |
| CN106913309B (en) * | 2015-07-31 | 2018-07-31 | 浙江大学 | Based on single all -fiber endoscopic OCT probe for drawing wimble structure |
| CN108324249A (en) * | 2018-02-07 | 2018-07-27 | 华南师范大学 | Optical coupled and photo-acoustic excitation intravascular photoacoustic imaging probe is realized based on conical fiber simultaneously |
| CN108324249B (en) * | 2018-02-07 | 2021-06-22 | 华南师范大学 | Intravascular photoacoustic imaging probe capable of simultaneously realizing optical coupling and photoacoustic excitation based on tapered optical fiber |
| CN109938679A (en) * | 2019-03-29 | 2019-06-28 | 杭州好克光电仪器有限公司 | Endoscope with protecting pipe |
| CN109938679B (en) * | 2019-03-29 | 2023-07-25 | 杭州好克光电仪器有限公司 | Endoscope with protective sleeve |
| CN112842270A (en) * | 2021-01-06 | 2021-05-28 | 浙江大学 | Focal depth expansion probe based on high-order mode energy regulation |
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|---|---|
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