CN104825120A - Optical clock signal generation system and method used in OCT (Optical Coherence Tomography) endoscopic scanning imaging system - Google Patents
Optical clock signal generation system and method used in OCT (Optical Coherence Tomography) endoscopic scanning imaging system Download PDFInfo
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Abstract
The invention provides an optical clock module and a signal generation method thereof used in an OCT (Optical Coherence Tomography) endoscopic scanning imaging system. The optical clock module comprises an interference module, a detector module and an optical clock conversion circuit module, wherein the optical clock conversion circuit module comprises a wideband 90-degree phase shifter, a zero-crossing comparator, a circuit formed by an exclusive-OR gate and an OR gate, and an optical clock signal output module. The invention also provides the OCT endoscopic scanning imaging system comprising the optical clock module. According to the invention, the conversion from an MZI (Mach Zehnder Interferometer) optical interference signal to an optical clock signal with uniformity on frequency domain and frequency variation on time domain is realized, the requirement on a sampling and processing system is reduced, the collection of redundant information is reduced, and the load of a storage system is reduced, so that the integration level of the whole OCT system is improved, and the system cost is reduced.
Description
Technical field
The present invention relates to sweeping laser technical field and optical coherence tomography scanning imagery field, particularly relate to a kind of being applied to and use the optical coherence tomography scanning imaging system of frequency swept laser, provide a kind of and effectively can reduce total sampled data output, the optical clock signal generation systems of simplification subsequent digital signal processing requirements and method.
Background technology
Optical coherence tomography scanning imagery (Optical Coherence Tomography, be called for short OCT), be widely used in ophthalmic diagnosis field, this technology is based upon on the basis of optics, electronics and computer technology science, it is the novel imaging technique that light harvesting electricity and the multinomial front subject such as high-speed data acquisition and image procossing are integrated, OCT relies on it have the advantage such as high-resolution, high speed imaging and enjoy the concern of people, and starts to be paid attention to and apply with clinical diagnosis field biomedical.
Compared with other imaging modes such as existing CT, ultrasonic, MRI, OCT has high resolution, and compared with traditional laser confocal microscope, the imaging depth of OCT has obvious advantage.The core technology of traditional optical probe mostly adopts fibre bundle to carry out light conduction and carries out imaging, or adopt CCD technology to carry out imaging, this type of inner peeping type probe only can detect the pathological changes of tissue surface, but the symptom of early-stage cancer occurs in the degree of depth of below epidermis 1-3 millimeter, therefore in traditional optical, pry head just seems unable to do what one wishes.Also have at present and undertaken spying upon head in medical imaging by ultrasonic principle, although can obtain the darker organizational information in below biological tissue top layer, resolution is only a millimeter magnitude, easily causes fail to pinpoint a disease in diagnosis early stage cancer.
Inner peeping type OCT technology is born and a flourish OCT branch technique with OCT technology development for nearly ten years, its core objective is under the prerequisite not reducing resolution, OCT optical imaging apparatus is microminiaturized, provides the high-resolution OCT image of inside of human body internal organs tube chamber.This technology extends the application of OCT technology greatly, makes OCT check object develop into human body viscera by body surface organ or biopsy samples, as blood vessel, digestive tract and respiratory tract etc.At present at clinicing aspect, OCT endoscopic technique is in inspection atherosclerosis and check that intravascular stent is laid in situation etc. and had preliminary application.
Traditional OCT system is time domain OCT system (TD-OCT), and the scanning speed of time domain OCT system generally cannot exceed 2000 lines per second, thus limits image taking speed.In recent years, second filial generation frequency domain OCT (FD-OCT) due to its scanning speed fast, detectivity advantages of higher, obtains more and more general attention.And in frequency domain OCT, adopt the frequency sweep OCT (SS-OCT) of high speed frequency swept laser then to have the advantages such as detection light path is simple, detectivity decay is little, be widely used.
In FD-OCT, for obtaining deep image information, picture signal needs to be uniformly distributed on frequency domain before carrying out Fourier transform.And in SS-OCT, due to the scan characteristic of frequency swept laser, the original image signal of uniform sampling in time domain directly obtained by high speed analog-digital conversion capture card does not meet this condition, this just requires to carry out over-sampling to original image signal, then utilize the mode of Digital Signal Processing to carry out digital resampling to it, thus picture signal is uniformly distributed on frequency domain.Such sampling and signal processing method all very high for the requirement of sampling system and digital information processing system, also can obtain a lot of redundancy, thus increase the burden of storage system.In addition, digital resampling also can cause the reduction of Signal-to-Noise, and causes detectivity to decay change greatly, causes clear picture degree to reduce.
Therefore, the signal that can either realize after the collection of high speed analog-digital conversion capture card is uniformly distributed at frequency domain, the requirement for sampling system and digital information processing system can be reduced again, reduce costs and ensure clear picture, be that inner peeping type OCT system is better applied to the fields such as blood vessel, digestive tract and respiratory tract, and obtain the key of deep image information.
Summary of the invention
In order to solve the above-mentioned technical problem existed in prior art, the object of this invention is to provide and a kind ofly in OCT, peep the optical clock module used in scanning imaging system, described optical clock module comprises intervention module, detector module and optical clock conversion circuit module, wherein, described intervention module can adopt optical fiber type Mach-Zeng Deer interferometer (MZI) or optical fiber type Michelson (Michelson) interferometer structure.Wherein Mach-Zeng Deer interferometer structure is primarily of two fiber couplers, two optical fiber circulators and two optical fiber polarization controller compositions, wherein first fiber coupler generally adopts asymmetric fiber coupler, by most of Laser output to the miniature probe of sample arm; In reference arm and sample arm, all place an optical fiber circulator reflect or back scattered optical signalling from two arms to collect; Second fiber coupler can adopt symmetrical expression 2 × 2 fiber coupler (namely splitting ratio is 50/50) to produce optical interference signal and to reduce DC common-mode signal, optical fiber polarization controller is placed symmetrically in reference arm and sample arm, for adjusting the polarization state of two arms to obtain best optical interference signal.Michelson's interferometer structure is then made up of symmetrical expression 2 × 2 fiber coupler, an optical fiber circulator and two optical Polarized Beam Controller, first sweeping laser is entering fiber coupler after optical fiber circulator, interference signal is being produced through same fiber coupler from reference arm and sample arm reflection or back scattered optical signalling, optical fiber polarization controller is placed symmetrically in reference arm and sample arm, for adjusting the polarization state of two arms to obtain best optical interference signal.The advantage of Mach-Zeng Deer interferometer (MZI) is that symmetrical configuration, dispersion management are simple, detectivity is high.The advantage of Michelson (Michelson) interferometer is that structure is simple and can not introduces polarization mode dispersion (PMD), both something in commons are that the optical path difference in the middle of two arms determines the free spectral range (FSR) that optical clock occurs, and also finally determine the maximum imaging depth of OCT image; Detector module can adopt adjustment of balance photodetector, is mainly used in converting the interferometric optical signal exported from intervention module to electrical signal.After being converted to electrical signal from the optical interference signal of MZI generation by a balance photodetector, through optical clock conversion circuit module, to be namely converted to through wideband 90-degree phase shifter, zero-crossing comparator, XOR gate or door and optical clock signal output module successively on frequency domain evenly, at the optical clock signal of time domain up-conversion rate.Wherein, wideband 90-degree phase shifter is mainly used in the phase shift 90 degree of MZI electrical signal, zero-crossing comparator is mainly used in the MZI electrical signal after to original MZI electrical signal and phase shift and carries out Zero-cross comparator to be converted to digital signal, and the zero point of MZI signal is uniformly distributed on frequency domain, rising edge or the trailing edge of the digital signal therefore produced after Zero-cross comparator are also uniformly distributed on frequency domain, XOR gate is mainly used in two dagital clock signals to merge, in a free spectral range (FSR), two clock signals are produced to obtain, add the maximum imaging depth of OCT not increasing under FSR prerequisite like this, decrease the shake (jitter) produced by optical signalling.And between two adjacent scanning, always there are some free times due to frequency swept laser, optical clock signal also needs by one or inserts the clock signal of some vacations to ensure that high speed analog-digital conversion capture card can normally work in blank space, or door achieves the function merged with false clock signal by true optical clock signal, optical clock signal output module is mainly used in the true optical clock signal after by merging and is transported to data acquisition module with false clock signal.
Another object of the present invention is to provide a kind ofly peeps the optical clock signal method for generation used in scanning imaging system in OCT, and comprise the following steps: a, intervention module carries out spectral interference, coupling to the laser entered, and is transferred to detector module; B, described detector module converts the interferometric optical signal exported from intervention module to electrical signal, and outputs to optical clock conversion circuit; C, through the process of optical clock conversion circuit, thus obtains optical clock signal that is even on frequency domain, time domain up-conversion rate; D, optical clock output module realizes optical clock signal that is even on frequency domain, time domain up-conversion rate.Wherein, described optical clock conversion circuit processing procedure comprises the following steps: the first step, a MZI electrical signal part through detector module conversion directly proceeds to zero-crossing comparator through wideband 90-degree phase shifter, and another part MZI electrical signal directly proceeds to zero-crossing comparator; Second step, described wideband 90-degree phase shifter makes the phase shift 90 degree of the electrical signal proceeding to wideband 90-degree phase shifter; Described digital signal, to there is phase shift and MZI electrical signal that phase shift do not occur is carried out Zero-cross comparator and is converted to digital signal, is then proceeded to XOR gate by zero-crossing comparator described in the 3rd step; 4th step, two dagital clock signals after zero-crossing comparator conversion are merged into true optical clock signal and are proceeded to or door again by described XOR gate; 5th step, true optical clock signal described in described or goalkeeper merges with false optical clock signal and proceeds to optical clock output module again.
Another object of the present invention is to provide in a kind of OCT and peeps scanning imaging system, comprise sweeping laser module, data acquisition module, data processing module, image display, actuator, OCT miniature probe and foley's tube, inflation/deflation equipment and described optical clock module, wherein:
Described sweeping laser module comprises high speed frequency swept laser, fibre optic isolater and fiber coupler, the optical signalling exported and subsequent optical path is isolated from frequency swept laser, and the optical signalling interference laser preventing subsequent optical path from returning normally works; Described data acquisition module can adopt high speed analog-digital conversion capture card, and the optical clock signal mainly exported with optical clock module gathers original image signal for benchmark, and is supplied to data processing module and processes; Described data processing module adopts the chip (as CPU, GPGPU, DSP, FPGA etc.) with digital signal processing capability, is mainly used in processing primary signal and being converted into final picture signal; Described image display is mainly used in display image signals and is responsible for post processing and the surveying work of image; Described actuator is made up of fiber rotation connector, motor and motorized precision translation stage, electric rotating machine in actuator drives OCT miniature probe to carry out rotation sweep, motorized precision translation stage drives actuator to move toward a direction simultaneously, at this moment the rotation sweep data got and translation stage mobile data are rebuild by software, namely produce 3D rendering; Described OCT miniature probe is mainly used in entering inside of human body internal organs to transmit sweeping laser and the optical signalling of collection backscattering from biological tissue; Described foley's tube, for expanding inside of human body internal organs pipeline, is eliminated gauffer and OCT miniature probe is stable at balloon center; Described inflation/deflation equipment is mainly used in expansion of balloon catheter.Described optical clock module is used by peeping in OCT in scanning imaging system, the requirement to data Collection & Processing System can be reduced, and reduce the collection of redundancy, alleviate the burden of storage system, thus improve the integrated level of whole OCT system, and then reduce system cost, and the signal to noise ratio of picture signal can also be improved, reduce detectivity decay, thus improve the definition of image.
Preferably, described OCT miniature probe comprises single-mode fiber, is enclosed within bourdon tube; Lens subassembly, make to be gathered in predetermined operating distance place by the light of spread fiber, described lens subassembly comprises Glass rod and GRIN Lens, can be changed the operating distance of OCT miniature probe by the gummed distance changing Glass rod and single-mode fiber; By the gummed of GRIN Lens and Glass rod, increase the clear aperature of GRIN Lens, and then improve numerical aperture and the lateral resolution of OCT probe.Described OCT miniature probe also can comprise reflecting mirror, support stainless steel tube and fluting stainless steel tube, and these optical element end face optical glue are glued together.
Wherein, described single-mode fiber one end is with sonet standard joint; this joint can be connected with the fiber spinning end of OCT system; described single-mode fiber is enclosed within bourdon tube and (is covered with PTFE film); bourdon tube can available protecting single-mode fiber; reduce resistance when probe rotates; make described OCT miniature probe entire scan more steady and smooth; described sonet standard joint is with support stainless steel tube; this stainless steel tube plays a supportive role when OCT miniature probe scans, more steady when making whole probe rotation sweep.The other end of described single-mode fiber is inclined-plane, also be that Glass rod one end end face on inclined-plane glues together with same, the inclination of cemented surface effectively reduces the interference of reflected light to flashlight, can change the operating distance of OCT miniature probe to reach required expection operating distance by the gummed distance changing Glass rod and single-mode fiber.The other end of described Glass rod and described GRIN Lens are packaged in after gluing together with 0 ° of angle end face slots in stainless steel tube, the use of Glass rod not only increases the operating distance of miniature probe, and increase the numerical aperture of miniature probe, and the increase of numerical aperture also causes the raising of lateral resolution, this design simultaneously has also shortened the length of GRIN Lens greatly, ensure that the curved property of the mistake of miniature probe, make whole miniature probe can directly enter human body esophagus by endoscopic forceps channel together with conduit.Described GRIN Lens and described Glass rod glue together, the face that wherein GRIN Lens contacts with air is coated with anti-reflection film, the reflection of light between optical surface can be reduced and increase light transmission, thus reduce because the reflected light of optical surface is on the impact of flashlight, improve the sensitivity of OCT miniature probe.The angle on the gummed inclined-plane of described single-mode fiber and Glass rod is 4 °-12 °.The reflecting surface of described reflecting mirror is packaged in stainless steel tube towards stainless steel tube otch, in order to reduce the astigmatism of light source by cylindrical interior pipe to the impact of imaging, reflecting mirror herein can design cylindrical mirror according to the cylindrical internal-and external diameter of interior pipe and the refractive index of inner tube material, the astigmatism impact of pipe in offsetting, correct the shape of hot spot, reach the object improving image quality.
Preferably, described foley's tube comprises: handle, and an interface of described handle is HPI, and another interface is ventilation interface; Double lumen tube, described double lumen tube can allow OCT optic probe to pass through; Sacculus, the front end shutoff of described sacculus and sacculus has scale; Interior pipe, the concentricity of described interior pipe and described sacculus departs from and is no more than 200 microns under 3 atmospheric pressure; Soft head, described soft head is solid construction, and wherein, described double lumen tube one end is connected with described handle, and the other end is connected with one end of described interior pipe and described sacculus, and described sacculus is connected with described soft head with the other end of described interior pipe.
Traditional foley's tube needs seal wire to support and guiding, and seal wire diameter is generally 0.018in, 0.035in, 0.014in, 0.038in, and foley's tube of the present invention can by the OCT optics miniature probe of 0.055in.Described sacculus there is ink printing scale, line thickness≤0.1mm, the direction of scanning probe can be distinguished, the scanning that both can not affect normal picture judges also to tell scanning position on a display screen simultaneously, described sacculus front end shutoff, prevent from body fluid from entering to impact optical scanning, adopt flexible material again simultaneously, patient's esophagus can not be scratched.The use pressure of sacculus is 3 atmospheric pressure, can not damage normal esophageal at low pressures, simultaneously the heat setting process of sacculus and welding procedure can ensure that the concentricity of pipe and sacculus under 3 atmospheric pressure in departs from and be no more than 200 microns, are convenient to optical imagery.Described soft head is solid construction, can prevent body fluid from entering.Described double lumen tube is connected with described handle by UV viscose glue, and other each parts all adopt welding procedure to connect.Described inner tube length is according to the length fixed length of described sacculus, and it is shorter in length than described sacculus, when described sacculus welds with described soft head, certain distance is pushed away by under described sacculus, make it concordant with interior pipe and fixing after weld, make sacculus when full, have one to extend surplus, thus mate the stretching of interior pipe and keep with one heart.Because interior Guan Taihou can affect the definition of scanogram, too thin, can affect rotation and the concentricity of probe, therefore described interior pipe is the design of OCT miniature probe specially, and inner tube diameter is 1.4mm, and external diameter is 1.65mm.In addition, in the present invention, handle material can adopt Merlon, and double lumen tube and soft head material can adopt block polyetheramides, and sacculus and inner tube material can adopt nylon and polymer-modified.
Preferably, inflation/deflation equipment is applied in described OCT and peeps scanning imaging system, namely sweeping laser module, data acquisition module, data processing module, image display, actuator, OCT miniature probe and foley's tube, described optical clock module and inflation/deflation equipment is comprised, described inflation/deflation equipment is automatic inflatable/air equipment, and described automatic inflatable/air equipment comprises: control and display module, air pump, inflation/deflation electromagnetic valve, pressure transducer, explosion-proof pressure sensor, mechanical pressure switches.Described automatic inflatable/air equipment achieves automatic inflating and air-breathing; and there is the function setting different pneumatic parameter; can carry out inflation/deflation to the sacculus of different size, equipment is stopping inflation after reaching the atmospheric pressure value of setting in inflated process, and has over-voltage protecting function.Its attainable effect is: first, eliminates the operation of doctor to the manual inflation/deflation of sacculus, shortens the time of doctor's inflation/deflation, and improve safety, avoids the risk that sacculus overcharges blast; Secondly, accurate air pressure controls the shape coincidence after making inflated and is guaranteed, due to the shape sensitive of the scanned object that optical imagery is propped up for sacculus, this is just carried out the repeatability of Multiple-Scan better to same by sweep object, and doctor can compare for the view data after scanning; Again, when emergency process, while can realizing automatic deflation, doctor does other operation.
Preferably, utilize general image processor (GPGPU) in OCT, peep in scanning imaging system the method processing OCT signal, data acquisition that the method comprises (1); (2) data transmission; (3) date processing; (4) image display four, storehouse step is passed to.
Wherein, (1) data acquisition, the present invention obtains FD-OCT initial data by outside collecting device;
(2) data transmission, the FD-OCT initial data obtained in data collection steps is placed in computer system or embedded system memory, these data are deposited in Installed System Memory in units of frame, after meeting certain condition (one frames as enough in data accumulation or multiframe), these data can be passed through data/address bus (as PCIExpress) and transfer in the device memory of general image processor; Because bus transfer speed is relatively slow, while transmission data, the OCT initial data that the last time transfers in device memory by general image processor carries out parallel processing.This kind of method has efficient Parallel signal processing ability, can realize Real-time digital signal processing, greatly improve efficiency of transmission, save bus resource;
(3) date processing, the Digital Signal Processing of carrying out in general image processor is divided into three steps: a dimension word resampling, one dimension fast fourier transform (FFT) and calculate amplitude normalization.Wherein realize a quick one dimension cubic interpolation to improve the precision of resampling by two sublinear texture lookups in a dimension word resampling steps;
(4) image display storehouse is passed to, the data placement handled well is in the internal memory in image display storehouse, image display storehouse can directly be called, without the need to passing through bus transfer again, greatly improve efficiency of transmission, save bus resource, there is efficient Parallel signal processing ability, realize Real-time digital signal processing, portable high, can seamless combination owing to showing storehouse with popular image, also improve the motility (such as: post processing can also be carried out by general image processor to image) of software display, lower hardware and software development cost can be realized.
Pass through the present invention, to achieve from MZI optical interference signal to frequency domain evenly, the conversion of the optical clock signal of time domain up-conversion rate, reduce the requirement to sampling and processing system, and reduce the collection of redundancy, alleviate the burden of storage system, thus improve the integrated level of whole OCT system, reduce system cost.
Accompanying drawing explanation
Fig. 1 is optical clock module diagram of the present invention;
Fig. 2 is optical clock signal generating process schematic diagram of the present invention;
Fig. 3 peeps scanning imaging system schematic diagram in the OCT with optical clock module of the present invention;
Fig. 4 is OCT miniature probe of the present invention component diagram in kind;
Fig. 5 is OCT miniature probe key position amplification profile of the present invention;
Fig. 6 is balloon catheter structure schematic diagram of the present invention;
Fig. 7 is inflation/deflation device structure schematic diagram of the present invention;
Fig. 8 is inflation/deflation equipment workflow diagram of the present invention;
Fig. 9 is FD-OCT signal processing step of the present invention;
Figure 10 is that GPGPU data of the present invention transmission, with signal processing is parallel, schematic diagram occurs;
Figure 11 is whole implementation structure chart of the present invention;
Figure 12 is OCT miniature probe operating distance of the present invention, gummed distance and lateral resolution curve relation figure;
Figure 13 is healthy animal esophagus scintigram of the present invention;
Figure 14 is healthy animal esophagus scintigram partial enlarged drawing of the present invention;
Figure 15 is healthy animal esophagus 3D rendering of the present invention.
drawing reference numeral explanation
1, single-mode fiber, 2, bourdon tube, 3, Glass rod, 4, GRIN Lens, 5, reflecting mirror, 6, fluting stainless steel tube, 7, support stainless steel tube, 8, soft head, 9, interior pipe, 10, sacculus, 11, double lumen tube, 12, handle, 13, ventilation interface, 14, HPI,
81, squamous epithelial layer (SE), 82, lamina propria (LP), 83, muscularis mucosae (MM), 84, tela submucosa (SM), 85, intrinsic basic unit (MP),
91, after wideband 90-degree phase shifter, there is the MZI electrical signal of 90 degree of phase shift, 92, there is not the MZI electrical signal of phase shift, 93, signal 91 carries out the digital signal after Zero-cross comparator, 94, signal 92 carries out the digital signal after Zero-cross comparator, 95, false clock signal, 96, the signal of digital signal 93 and 94 after XOR gate merges
101, air pump, 102, inflation electromagnetic valve, 103, pressure transducer, 104, choke valve, 105, pressure transducer, 106, explosion-proof pressure sensor, 107, suction solenoid valve, 108, mechanical pressure switches.
Detailed description of the invention
In order to make object of the present invention, technical scheme and advantage clearly understand, below in conjunction with drawings and Examples, the present invention is further elaborated.Should be appreciated that specific embodiment described herein only in order to explain the present invention, be not intended to limit the present invention.
Below in conjunction with accompanying drawing, technical solution of the present invention is described in detail.
Embodiment 1
As shown in Figure 1, a kind ofly in OCT, peep the optical clock module used in scanning imaging system, it comprises intervention module, detector module and optical clock conversion circuit module, and described optical clock conversion circuit module comprises circuit and the optical clock signal output module of wideband 90-degree phase shifter, zero-crossing comparator and XOR gate or door composition.Wherein, intervention module adopts all-fiber formula Mach-Zender interferometer (MZI) structure, form primarily of two fiber couplers, wherein second bonder is symmetrical expression 2 × 2 fiber coupler, first two-way light is punished at the first fiber coupler, this two-way light, respectively through the first optical fiber of two sections of fixed light path differences and the second optical fiber, interferes at the second fiber coupler place.Detector module is made up of adjustment of balance photodetector, is mainly used in converting the interferometric optical signal exported from intervention module to electrical signal.A MZI electrical signal part after detector module conversion is transferred to wideband 90-degree phase shifter, another part is transferred to zero-crossing comparator, there is the phase shift of 90 degree in the electrical signal being transferred to wideband 90-degree phase shifter, zero-crossing comparator is mainly used in carrying out Zero-cross comparator to be converted to digital signal to generation phase shift and signal that phase shift do not occur.XOR gate is mainly used in two dagital clock signals to merge, to obtain two clock signals produced in a free spectral range (FSR), add the maximum imaging depth of OCT not increasing under FSR prerequisite like this, decrease the shake (jitter) that optical signalling produces.Because frequency swept laser always exists some free times between two adjacent scanning, optical clock signal also needs by one or inserts the clock signal of some vacations to ensure that high speed analog-digital conversion capture card can normally work in blank space, or door achieves the function merged with false clock signal by true optical clock signal.Optical clock signal output module is mainly used in the true optical clock signal after by merging and is transported to data acquisition module with false clock signal.
As shown in Figure 2, 91 is the MZI electrical signal that 90 degree of phase shift occur after wideband 90-degree phase shifter, 92 for there is not the MZI electrical signal of phase shift, 93 carry out the digital signal after Zero-cross comparator for there is the MZI signal 91 of phase shift, 94 carry out the digital signal after Zero-cross comparator for the MZI signal 92 that phase shift do not occur, because the zero point of MZI signal is uniformly distributed on frequency domain, rising edge or the trailing edge of the digital signal therefore produced after Zero-cross comparator are also uniformly distributed on frequency domain, 96 is the signal of digital signal 93 and 94 after XOR gate merges that frequency domain is evenly distributed, 95 is false clock signal, 95 and 96 form the optical clock signal after warp or door merging jointly.
Embodiment 2
As shown in Figure 3, scanning imaging system is peeped in a kind of OCT, comprise sweeping laser module, optical clock module, data acquisition module, data processing module, image display, actuator, OCT miniature probe and foley's tube and inflation/deflation equipment, wherein: described optical clock module as shown in Figure 1, comprise intervention module, detector module and optical clock conversion circuit module, described optical clock conversion circuit module comprises wideband 90-degree phase shifter, zero-crossing comparator and XOR gate, or door composition circuit and optical clock signal output module, after being converted to electrical signal from the optical interference signal of MZI generation by a balance photodetector, through one by wideband 90-degree phase shifter, the circuit of zero-crossing comparator and XOR gate composition and to be converted on frequency domain evenly, at the optical clock signal of time domain up-conversion rate, or the true optical clock signal of goalkeeper merges the normal work with high speed analog-digital conversion capture card with false clock signal.
Described sweeping laser module includes high speed frequency swept laser, fibre optic isolater and fiber coupler, the optical signalling exported from frequency swept laser and subsequent optical path are isolated, the optical signalling interference laser preventing subsequent optical path from returning normally works, and the output of sub-fraction sweeping laser is separated to optical clock module, most of laser continues to export; Described optical clock module comprises intervention module, detector module and optical clock conversion circuit module, to be mainly used in obtaining on frequency domain evenly, at the optical clock signal of time domain up-conversion rate; Described data acquisition module can adopt high speed analog-digital conversion capture card, and the optical clock signal mainly exported with optical clock module gathers original image signal for benchmark, and is supplied to data processing module and processes; Described data processing module is the chip (as CPU, GPGPU, DSP, FPGA etc.) with digital signal processing capability, is mainly used in processing primary signal and being converted into final picture signal; Described image display is mainly used in display image signals and is responsible for post processing and the surveying work of image; Described actuator is made up of fiber rotation connector, motor and motorized precision translation stage, is mainly used in driving the scanning of OCT miniature probe mechanical spiral to obtain OCT image; Described OCT miniature probe is mainly used in entering inside of human body internal organs to transmit sweeping laser and the optical signalling of collection backscattering from biological tissue; Described foley's tube, for expanding inside of human body internal organs pipeline, is eliminated gauffer and OCT miniature probe is stable at balloon center; Described inflation/deflation equipment is mainly used in expansion of balloon catheter.
Embodiment 3
Scanning imaging system is peeped in a kind of OCT, similar to embodiment 2, difference be described OCT miniature probe as shown in Figure 4 and Figure 5: single-mode fiber 1 is enclosed within bourdon tube 2, and bourdon tube 2, while the optical fiber of available protecting fragility, reduces resistance when probe rotates; Glass rod 3 one end and GRIN Lens 4 zero degree edged surface glue together, the other end and single-mode fiber 1 tilt to glue together, the operating distance of OCT probe can be changed by the gummed distance changing Glass rod 3 and single-mode fiber 1 two end faces to reach the operating distance required by expection, and then improve numerical aperture and the lateral resolution of OCT probe; Reflecting mirror 5 is cylindrical mirror and is packaged in fluting stainless steel tube 6, and the reflecting surface of reflecting mirror 5 is towards the otch of fluting stainless steel tube 6, can reduce the astigmatism of light source by cylindrical interior pipe to the impact of imaging with this.
As Fig. 4 and Fig. 5, peep the OCT miniature probe of scanning imaging system in a kind of OCT, comprise single-mode fiber 1, bourdon tube 2, Glass rod 3, GRIN Lens 4, reflecting mirror 5, fluting stainless steel tube 6 and support stainless steel tube 7, these optical element end face optical glue are glued together.Specifically, reflecting mirror 5 is loaded in fluting stainless steel tube 6, be then placed in frock and put A/B glue, then put UV glue under the microscope, Glass rod 3 and GRIN Lens 4 are assembled; Single-mode fiber 1 is penetrated in bourdon tube 2, again the Glass rod 3 assembled and GRIN Lens 4, single-mode fiber 1 and bourdon tube 2 are used a UV glue assembling, finally put into by the bourdon tube assembly after assembling in fluting stainless steel tube 6, edge voids place uses A/B glue to fill up.
Single-mode fiber 1 outer cover has stainless steel spring pipe 2 (being covered with PTFE film), while the optical fiber of available protecting fragility, reduces resistance when probe rotates, makes miniature probe scan more steady and smooth.Supporting the Main Function of stainless steel tube 7 is play a supportive role when OCT probe scans, and more steady when making whole probe rotation sweep, the notch of fluting stainless steel tube 6 can make light beam be irradiated on sample by this notch.
Anti-reflection film can reduce the reflection of light between optical surface and increase light transmission, thus reduce because the reflected light of optical surface is on the impact of flashlight, therefore, in the present embodiment, the face that GRIN Lens 4 contacts with air is coated with anti-reflection film, Glass rod 3 and GRIN Lens 4 zero degree edged surface glue together simultaneously, improve sensitivity and the resolution of miniature probe.The other end of Glass rod 3 and the cemented surface of single-mode fiber 1 have certain angle of inclination, in the present embodiment, the angle of inclination of cemented surface can be 8 ° herein, the inclination of cemented surface effectively reduces the interference of reflected light to flashlight, generally, the operating distance of OCT probe can be changed by the gummed distance changing these two end faces to reach the operating distance required by expection.Because 45° angle installs reflecting mirror 5, make incident ray vertical with reflection ray thus cause light to disturb, in the present embodiment, 40 ° of corner reflectors 5 are installed in miniature probe front end, reflecting mirror 5 is packaged in fluting stainless steel tube 6, and the reflecting surface of reflecting mirror 5 is towards the otch of fluting stainless steel tube 6, simultaneously in order to reduce the astigmatism of light source by cylindrical interior pipe to the impact of imaging, in the present embodiment, reflecting mirror herein designs cylindrical mirror according to the cylindrical internal-and external diameter of interior pipe and the refractive index of inner tube material.
Embodiment 4
Peep scanning imaging system in a kind of OCT, similar to embodiment 2 or 3, difference be described foley's tube as shown in Figure 6, it includes: handle 12, and an interface of handle 12 is HPI 14, and another interface is ventilation interface 13; Double lumen tube 11, can allow OCT optic probe to pass through; Sacculus 10, the front end shutoff of sacculus 10 and sacculus has scale; Interior pipe 9, interior pipe 9 departs from the concentricity of sacculus 10 and is no more than 200 microns under 3 atmospheric pressure; Soft 8 is solid construction, wherein, double lumen tube 11 one end is connected with handle 12, and the other end is connected with one end of interior pipe 9 and sacculus 10, and sacculus 10 is connected with soft 8 with the other end of interior pipe 9, double lumen tube 11 is connected with handle 12 by UV viscose glue, and other each several parts are all connected by the mode of welding.
Handle 12 material is Merlon, and double lumen tube 11 and soft 8 materials are block polyetheramides, and sacculus 10 and interior pipe 9 material are nylon and polymer-modified.
Sacculus 10 has ink printing scale, line thickness≤0.1mm, can distinguish the direction of scanning probe, the scanning that both can not affect normal picture judges also to tell scanning position on a display screen simultaneously.Double lumen tube 11 is printed on scale, and therefore, doctor can judge the position scanned.
Traditional foley's tube needs seal wire to support and guiding, and seal wire diameter is generally 0.018in, 0.035in, 0.014in, 0.038in, and in the present embodiment, the double lumen tube 11 of OCT foley's tube can by 0.055in OCT optic probe.Because interior Guan Taihou can affect the definition of scanogram, too thin, can affect rotation and the concentricity of probe, in the present embodiment, pipe 9 internal diameter is 1.4mm, and external diameter is 1.65mm, is OCT probe designs specially.Described inner tube length is according to the length fixed length of described sacculus, and it is shorter in length than described sacculus, when described sacculus welds with described soft head, certain distance is pushed away by under described sacculus, make it concordant with interior pipe and fixing after weld, make sacculus when full, have one to extend surplus, thus mate the stretching of interior pipe and keep with one heart.
Embodiment 5
Scanning imaging system is peeped in a kind of OCT, to embodiment 2,3 or 4 similar, difference is described inflation/deflation equipment is automatic inflatable/air equipment, as shown in Figure 7, described automatic inflatable/air equipment comprises: power pack, control and display section and air pump and control system part thereof, described air pump and control system part thereof comprise: air pump, inflation/deflation electromagnetic valve, choke valve, pressure transducer, explosion-proof pressure sensor, mechanical pressure switches.As shown in Figure 8, the use procedure of described automatic inflatable/air equipment comprises:
1) gas replenishment process: first user sets the parameters such as sacculus 10 air pressure, inflationtime, send inflation order, control system reads the data of pressure transducer 103,105, if be less than the air pressure of user's setting, then booster air pump 101, open inflation electromagnetic valve 102, choke valve 104, the value of feedback of pressure transducer 103,105 is read in real time in gas replenishment process, until be charged to the atmospheric pressure value of setting, close air pump 101, close choke valve 104, inflation electromagnetic valve 102;
2) deflation course: first user sets the parameters such as sacculus 10 air pressure, deflation time, control system reads the data of pressure transducer 105, if be greater than the air pressure of user's setting, then booster air pump 101, open suction solenoid valve 107, choke valve 104, read the value of feedback of pressure transducer 105 in deflation course in real time, until be drawn onto the atmospheric pressure value of setting, holding one's breath 101 pumps in pass, closes choke valve 104, suction solenoid valve 107.
In inflation/deflation process, system is monitored the value of feedback of explosion-proof pressure sensor 106 in real time, if exceed user's air pressure upper limit set value, then carries out software program protection immediately, closes air pump 101, and reports to the police; Mechanical pressure switches 108 is hardware protection, and as exceeded setting value, then switch opens, pressure release is protected.
Embodiment 6
Peep scanning imaging system in a kind of OCT, similar to embodiment 2-5, difference be utilize general image processor process OCT signal scheme as shown in Figure 9, comprise (1) data acquisition be connected successively; (2) data transmission; (3) date processing and (4) are passed to these steps of image display storehouse, wherein when data are transmitted because bus transfer speed is relatively slow, while transmission data, the OCT initial data that last time transfers in device memory by general image processor carries out parallel processing, and its parallel transmission and processing procedure are as shown in Figure 10; The process of date processing is divided into three steps: a dimension word resampling, one dimension fast fourier transform (FFT) and calculate amplitude normalization, wherein, a quick one dimension cubic interpolation is realized to improve the precision of resampling by two sublinear texture lookups in a dimension word resampling steps.
As shown in Figure 9, a kind of scheme of general image processor process OCT signal that utilizes comprises (1) data acquisition be connected successively; (2) data transmission; (3) date processing and (4) are passed to these steps of image display storehouse.
Wherein, (1) data acquisition, the present invention obtains FD-OCT initial data by outside collecting device;
(2) data transmission, the FD-OCT initial data obtained in data collection steps is placed in computer system or embedded system memory, these data are deposited in Installed System Memory in units of frame, after meeting certain condition (one frames as enough in data accumulation or multiframe), these data can be passed through data/address bus (as PCIExpress) and transfer in the device memory of general image processor (GPGPU); Because bus transfer speed is relatively slow, while transmission data, the OCT initial data that the last time transfers in device memory by general image processor carries out parallel processing.
Such as: as shown in Figure 10, while the initial data of the n-th frame is transferred to general image processor device internal memory, the initial data of the (n-1)th frame is carried out Digital Signal Processing simultaneously in general image processor, and frame synchronization is carried out after data transmission and process terminate, namely no matter be that data are transmitted or the reef knot Shu Houzai completed after wait is carried out the operation of next frame by the side that date processing completes, effectively can be improved the data processing speed of general image processor by this parallel signal transmission/transaction module.
(3) date processing, as shown in Figure 9, the Digital Signal Processing of carrying out in general image processor is divided into three steps: a dimension word resampling, one dimension fast fourier transform (FFT) and calculate amplitude normalization.Wherein digital resampling can pass through the built-in texture lookups functional realiey of image processor (GPU), the built-in texture lookups function of image processor can realize two-dimensional linear interpolation automatically to interpolation, and the texture lookups module of image processor has special hardware optimization to interpolation, faster relative to general general image processor interpolation speed, particularly for the non-equidistant interpolation in OCT signal processing; By accurately arranging a dimension search a little, can by the built-in texture lookups functional realiey one-dimensional linear interpolation of image processor.On this basis, a quick one dimension cubic interpolation is realized by two sublinear texture lookups, thus to improve the precision of resampling, because texture lookups module has carried out special optimization to non-equidistant interpolation, this method implements on general image processor than direct cubic interpolation that amount of calculation is less, computational efficiency is higher; FFT can be realized by the numerical computations storehouse (cuFFT storehouse or OpenCL FFT storehouse as nVidia) of common commercialization based on image processor; Calculating amplitude normalization then can realize by oneself writing image processor program, and the CUDA storehouse that nVidia such as can be used to provide realizes the quick traversal of 2-D data to write corresponding kernel function (kernelfunction) to realize amplitude and normalization calculates.
(4) image display storehouse is passed to, the data placement handled well is in the internal memory in image display storehouse, image display storehouse can directly be called, without the need to passing through bus transfer again, greatly improve efficiency of transmission, save bus resource, there is efficient Parallel signal processing ability, realize Real-time digital signal processing, portable high, can seamless combination owing to showing storehouse with popular image, also improve the motility (such as: post processing can also be carried out by general image processor to image) of software display, lower hardware and software development cost can be realized.
Embodiment 7
As shown in figure 11, a kind of miniature probe carrying out OCT image scanning for human body esophagus, miniature probe is inserted until in sacculus pipe 9 from balloon proximal handle guidewire lumen, sacculus handle ventilation interface 13 is connected to automatic inflation pump (not shown), nominal pressure is inflated to by sacculus 10, so that extended by esophagus, described sacculus 10 and interior pipe 9 are all that optically transparent material is made, and have fabulous light transmission.The effect of sacculus 10 is that expansion esophagus is to reduce esophagus wrinkle and to be fixed within its operating distance scope by OCT miniature probe.The radius that sacculus 10 is expanded is greatly between 8-10mm, and this is also the radius after esophagus launches completely, and therefore, a relatively large operating distance (greatly about 8-10mm) is the characteristic that OCT miniature probe must have.
Glass rod 3 is devised especially in the present embodiment, mention in aforementioned that the gummed distance changing Glass rod 3 and single-mode fiber 1 can change the operating distance of miniature probe, this routine miniature probe is used for human body esophagus, operating distance, greatly about 8-10mm, should be less than 0.3mm by the gummed distance on calculating and tested glass rod 3 and single-mode fiber 1 two sides.The design ap-plication of Glass rod 3 not only makes OCT miniature probe can be operated within the scope of longer operating distance, can also change numerical aperture and the lateral resolution of miniature probe.
The clear aperature relation of numerical aperture and optical element is as follows:
Wherein, D is the clear aperature of optical element, W.D is operating distance, N.A is numerical aperture, and when operating distance W.D. mono-timing, numerical aperture is directly proportional to the clear aperature (D) of optical element, due to the defect of the processing technique of GRIN Lens own, clear aperature can only reach about 80% of its diameter, and leading portion plays the effect of expanding after adding Glass rod, namely increases clear aperature.
The relation of resolution and numerical aperture is as follows:
Wherein, λ is lambda1-wavelength is definite value, and lateral resolution △ X is proportional to numerical aperture (N.A), and namely numerical aperture is larger, lateral resolution higher (numerical value is less).
In summary, the use of Glass rod 3 not only increases the operating distance of miniature probe, and increase the numerical aperture of miniature probe, and the increase of numerical aperture also causes the raising of lateral resolution, this design simultaneously, also shortened the length of GRIN Lens greatly, ensure that the curved property of the mistake of miniature probe, whole like this miniature probe still can directly enter human body esophagus by endoscopic forceps channel together with foley's tube.This design effectively, make the lateral resolution of probe be about 10-30 micron, operating distance can reach 8-10 millimeter, and the relation of the lateral resolution of operating distance and miniature probe is as Figure 12.The diameter of whole miniature probe is less than 1.5 millimeters, and as adopted diameter 1.0 millimeters of GRIN Lens, the diameter of whole miniature probe is less than 1.3 millimeters; As adopted diameter 0.7 millimeter of GRIN Lens, the diameter of whole miniature probe is less than 1.0 millimeters; As adopted diameter 0.5 millimeter of GRIN Lens, the diameter of whole miniature probe is less than 0.7 millimeter.
Figure 13 is the one section of healthy animal esophagus image obtained by OCT foley's tube endoscope, and picture size is 1200 transversal scanning number × 4096 longitudinal scannings, and sweep speed is 0.2cm/3s, and scale is 1mm.Figure 14 is the partial enlarged drawing of Figure 13 healthy animal esophagus image, recognizable layer comprises, and 81: squamous epithelial layer (SE), 82: lamina propria (LP), 83: muscularis mucosae (MM), 84: tela submucosa (SM) and 85: intrinsic basic unit (MP).Scan-data, for carry out luminal surface and depth scan by peeping scanning imaging system in OCT, is then carried out the healthy animal esophagus 3D rendering of software rebuild generation by Figure 15.
Be only the preferred implementation of the application described in upper, those skilled in the art understood or realizes the invention of the application.For these embodiments multiple amendment and combination will be apparent for a person skilled in the art, General Principle as defined herein when not departing from the spirit or scope of the application, can realize in other embodiments.Therefore, the application can not be limited in these embodiments shown in this article, but will meet the widest scope consistent with principle disclosed herein and features of novelty.
Claims (9)
1. in OCT, peep the optical clock module used in scanning imaging system, described optical clock module comprises intervention module, detector module and optical clock conversion circuit module, wherein,
Described intervention module is mainly carried out spectral interference to the laser entered and is coupled;
The interferometric optical signal that described detector module is mainly used in intervention module exports converts electrical signal to;
Described optical clock conversion circuit module comprises wideband 90-degree phase shifter, zero-crossing comparator, XOR gate or the door and optical clock signal output module that connect successively, electrical signal after the conversion of described detector module to be converted on frequency domain evenly by it, at the optical clock signal of time domain up-conversion rate, wherein
Described wideband 90-degree phase shifter makes the phase shift 90 degree of part MZI electrical signal;
Described zero-crossing comparator carries out Zero-cross comparator to original MZI electrical signal and the MZI electrical signal after there is phase shift and is converted to digital signal, and the digital signal after conversion is evenly distributed on frequency domain;
Described XOR gate is mainly used in two dagital clock signals after zero-crossing comparator conversion to merge;
Described or door is mainly used in true optical clock signal and false clock signal to merge;
Described optical clock signal output module is mainly used in the true optical clock signal after by merging and is transported to data acquisition module with false optical clock signal.
2. according to claim 1ly in OCT, peep the optical clock module used in scanning imaging system, it is characterized in that, described intervention module is all-fiber formula Mach-Zender interferometer structure, form primarily of two fiber couplers, wherein second bonder is symmetrical expression 2 × 2 fiber coupler.
3. according to claim 1ly in OCT, peep the optical clock module used in scanning imaging system, it is characterized in that, described intervention module is optical fiber type Michelson's interferometer structure, comprises symmetrical expression 2 × 2 fiber coupler, an optical fiber circulator and two optical Polarized Beam Controller.
4. in OCT, peep in scanning imaging system a signal generating method for the optical clock module used described in any one of claim 1 to 3, comprising:
A. intervention module carries out spectral interference, coupling to the laser entered, and is transferred to detector module;
B. described detector module converts the interferometric optical signal exported from intervention module to electrical signal, and outputs to optical clock conversion circuit;
C. optical clock conversion circuit processing signals, comprises the steps:
C1. a part of electrical signal directly proceeds to zero-crossing comparator through wideband 90-degree phase shifter, and another part electrical signal directly proceeds to zero-crossing comparator;
C2. described wideband 90-degree phase shifter makes the phase shift 90 degree of the electrical signal proceeding to wideband 90-degree phase shifter;
C3. to there is phase shift and MZI electrical signal that phase shift do not occur is carried out Zero-cross comparator and is converted to digital signal in described zero-crossing comparator, then described digital signal proceeded to XOR gate;
XOR gate described in c4 proceeds to or door after two dagital clock signals after zero-crossing comparator conversion are carried out merging into true optical signalling again;
C5. described or described in goalkeeper true optical clock signal merges with false clock signal and proceeds to optical clock signal output module again;
D. signal is transported to data acquisition module by described optical clock signal output module.
5. peep a scanning imaging system in OCT, comprise sweeping laser module, actuator, data acquisition module, data processing module, image display, OCT miniature probe and foley's tube, inflation/deflation equipment and the optical clock module described in any one of claims 1 to 3.
6. peep scanning imaging system in OCT according to claim 5, it is characterized in that, described actuator drives OCT miniature probe to carry out rotation sweep, can produce 3D rendering.
7. peep scanning imaging system in OCT according to claim 5, it is characterized in that, described foley's tube comprises:
Handle, an interface of described handle is HPI, and another interface is ventilation interface;
Double lumen tube, described double lumen tube can allow OCT optic probe to pass through;
Sacculus, the front end shutoff of described sacculus and sacculus has scale;
Interior pipe, the concentricity of described interior pipe and described sacculus departs from and is no more than 200 microns under 3 atmospheric pressure;
Soft head, described soft head is solid construction, wherein,
Described double lumen tube one end is connected with described handle, and the other end is connected with one end of described interior pipe and described sacculus, and described sacculus is connected with described soft head with the described interior pipe other end.
8. peep scanning imaging system in OCT according to claim 5, it is characterized in that, described inflation/deflation equipment is automatic inflatable/air equipment, and described automatic inflatable/air equipment comprises: control and display module, air pump, inflation/deflation electromagnetic valve, pressure transducer, explosion-proof pressure sensor, mechanical pressure switches.
9. peep scanning imaging system in the OCT according to any one of claim 5 to 8, it is characterized in that, peep in scanning imaging system the method processing OCT signal in OCT and comprise: a. data acquisition; B. data transmission; C. date processing; D. view data display storehouse is passed to; It is characterized in that, while transmission data, by general image processor, by the last time, the OCT initial data transferred in device memory carries out parallel processing, and is shown in the internal memory in storehouse in image by the data placement handled well.
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Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2016180291A1 (en) * | 2015-05-08 | 2016-11-17 | 南京微创医学科技有限公司 | Endoscopic oct microprobe, oct imaging system, and use method |
| WO2016180286A1 (en) * | 2015-05-08 | 2016-11-17 | 南京微创医学科技有限公司 | Optical-clock-signal generation system and method used in oct endoscopic scanning imaging system |
| WO2016180287A1 (en) * | 2015-05-08 | 2016-11-17 | 南京微创医学科技有限公司 | Method and system for processing oct signal using general-purpose graphics processing unit |
| CN108042125A (en) * | 2017-05-27 | 2018-05-18 | 天津海仁医疗技术有限公司 | A kind of high speed endoscopic optical coherent flow imaging system |
| CN108553088A (en) * | 2018-05-11 | 2018-09-21 | 苏州阿格斯医疗技术有限公司 | OCT systems |
| CN113872841A (en) * | 2021-09-23 | 2021-12-31 | 明峰医疗系统股份有限公司 | Self-recovery CT data transmission system and data transmission method |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN108986084B (en) * | 2018-06-28 | 2022-04-19 | 中山大学 | Novel OCT image display method |
| CN114331805B (en) * | 2021-12-27 | 2023-04-14 | 中国科学院苏州生物医学工程技术研究所 | OCT imaging method and system based on GPU |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3930203A (en) * | 1973-10-29 | 1975-12-30 | Siemens Ag | Circuit arrangement for adjusting the phase state of a timing signal |
| CN1709195A (en) * | 2005-06-24 | 2005-12-21 | 清华大学 | Real-time imaging optical coherent endoscope system |
| CN101600388A (en) * | 2007-01-10 | 2009-12-09 | 光学实验室成像公司 | The method and apparatus that is used for swept-source optical coherence tomography |
| CN103501682A (en) * | 2011-03-07 | 2014-01-08 | 智能医疗系统有限公司 | Balloon-equipped endoscopic devices and methods thereof |
| CN203953614U (en) * | 2014-06-19 | 2014-11-26 | 李健 | Per os choledochoscope guiding device |
| CN104220015A (en) * | 2012-04-13 | 2014-12-17 | 阿克拉伦特公司 | Balloon dilation catheter system for treatment and irrigation of the sinuses |
| CN204698494U (en) * | 2015-05-08 | 2015-10-14 | 南京微创医学科技有限公司 | The optical clock module used in scanning imaging system is peeped in OCT |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP6066901B2 (en) * | 2010-06-03 | 2017-01-25 | ザ ジェネラル ホスピタル コーポレイション | Method for apparatus and device for imaging structures in or in one or more luminal organs |
| CN104825120A (en) * | 2015-05-08 | 2015-08-12 | 南京微创医学科技有限公司 | Optical clock signal generation system and method used in OCT (Optical Coherence Tomography) endoscopic scanning imaging system |
| CN204636277U (en) * | 2015-05-08 | 2015-09-16 | 南京微创医学科技有限公司 | Scanning imaging system is peeped in the OCT with automatic inflatable/air equipment |
-
2015
- 2015-05-08 CN CN201510234293.4A patent/CN104825120A/en active Pending
-
2016
- 2016-05-06 WO PCT/CN2016/081340 patent/WO2016180286A1/en active Application Filing
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3930203A (en) * | 1973-10-29 | 1975-12-30 | Siemens Ag | Circuit arrangement for adjusting the phase state of a timing signal |
| CN1709195A (en) * | 2005-06-24 | 2005-12-21 | 清华大学 | Real-time imaging optical coherent endoscope system |
| CN101600388A (en) * | 2007-01-10 | 2009-12-09 | 光学实验室成像公司 | The method and apparatus that is used for swept-source optical coherence tomography |
| CN103501682A (en) * | 2011-03-07 | 2014-01-08 | 智能医疗系统有限公司 | Balloon-equipped endoscopic devices and methods thereof |
| CN104220015A (en) * | 2012-04-13 | 2014-12-17 | 阿克拉伦特公司 | Balloon dilation catheter system for treatment and irrigation of the sinuses |
| CN203953614U (en) * | 2014-06-19 | 2014-11-26 | 李健 | Per os choledochoscope guiding device |
| CN204698494U (en) * | 2015-05-08 | 2015-10-14 | 南京微创医学科技有限公司 | The optical clock module used in scanning imaging system is peeped in OCT |
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2016180291A1 (en) * | 2015-05-08 | 2016-11-17 | 南京微创医学科技有限公司 | Endoscopic oct microprobe, oct imaging system, and use method |
| WO2016180286A1 (en) * | 2015-05-08 | 2016-11-17 | 南京微创医学科技有限公司 | Optical-clock-signal generation system and method used in oct endoscopic scanning imaging system |
| WO2016180287A1 (en) * | 2015-05-08 | 2016-11-17 | 南京微创医学科技有限公司 | Method and system for processing oct signal using general-purpose graphics processing unit |
| CN108042125A (en) * | 2017-05-27 | 2018-05-18 | 天津海仁医疗技术有限公司 | A kind of high speed endoscopic optical coherent flow imaging system |
| CN108042125B (en) * | 2017-05-27 | 2023-04-21 | 天津恒宇医疗科技有限公司 | High-speed endoscopic optical coherent blood flow imaging system |
| CN108553088A (en) * | 2018-05-11 | 2018-09-21 | 苏州阿格斯医疗技术有限公司 | OCT systems |
| CN108553088B (en) * | 2018-05-11 | 2024-04-16 | 苏州阿格斯医疗技术有限公司 | OCT system |
| CN113872841A (en) * | 2021-09-23 | 2021-12-31 | 明峰医疗系统股份有限公司 | Self-recovery CT data transmission system and data transmission method |
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| WO2016180286A1 (en) | 2016-11-17 |
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