CN108042125A

CN108042125A - A kind of high speed endoscopic optical coherent flow imaging system

Info

Publication number: CN108042125A
Application number: CN201710391609.XA
Authority: CN
Inventors: 田洁
Original assignee: Tianjin Hengyu Medical Technology Co Ltd; Tianjin Hairen Medical Technology Co Ltd
Current assignee: Tianjin Hengyu Medical Technology Co ltd
Priority date: 2017-05-27
Filing date: 2017-05-27
Publication date: 2018-05-18
Anticipated expiration: 2037-05-27
Also published as: CN108042125B

Abstract

The invention discloses a kind of high speed endoscopic optical coherent flow imaging systems, it is characterised in that：The system comprises：Red laser, light source, interferometer, reference arm and sample arm, sacculus systems stabilisation, movement compensating algorithm, automatic clock switchover module, data acquisition and transport module, fiber coupler；Optical signal is divided into two-way, enter sample arm all the way, it is reference arm all the way, and the light that reference arm and sample arm are returned, incoming interferometer, optics rotation terminal, host computer image processing system, the present invention is based on the interior OCT systems for peeping blood flow detection can not only observe in-vivo tissue lesion morphological feature, can also diagnose tissue lower floor blood distribution situation.By tissue blood flow's imaging contexts, lesion information is diagnosed.

Description

A kind of high speed endoscopic optical coherent flow imaging system

【Technical field】

The present invention relates to a kind of imaging system, more particularly to a kind of high speed endoscopic optical coherent flow imaging system.

【Background technology】

OCT（Optical coherence tomography）, it is the new imaging technique generated in 90 years 20th century.The technology is in medical application It is upper that there are high-resolution, non-intrusion type imaging features.OCT can be divided into time domain OCT and frequency domain OCT, frequency domain OCT scan speed It is far longer than time domain OCT, has been substituted time domain OCT.Frequency domain OCT is different according to image-forming principle, and can be divided into SS-OCT (frequency sweeps ) and SD-OCT spectrum OCT OCT.SS-OCT is imaged using sweeping laser, and SD-OCT is imaged using grating cooperation CCD.

Endoscopic OCT and intravascular OCT are quickly grown in recent years, bright in the imaging of detection in-vivo tissue and intravascular imaging effect It is aobvious.But based on the interior OCT systems peeped, imaging of tissue is also only limitted at present.

Medically, the technology for based on blood flow detection diagnose some diseases plays the role of ever more important.Laser dissipates Spot blood flow imaging technology, Doppler's OCT blood flow detections technology, the angiographic imaging based on OCT.It is wherein emerging to be based on The Angiography of OCT is novel vascular imaging technique.Laser speckle is imaged, and resolution ratio is relatively low, can only observe bigger Blood vessel.Doppler flow inaging detects, and is limited by the influence of detection angles, when probe to the detection angle of skin close to it is vertical when its Effect is excessively poor.Angiography based on OCT then with high resolution, is imaged the advantages of being influenced from angle.

Union of wounded skin is studied using laser Doppler perfusion imaging by the Perimed companies of Sweden.Moor companies are based on Laser-Doppler evaluates burn blood flow detection.Laser speckle is imaged and laser-Doppler is all two-dimensional imaging, can only be seen The blood flow information of shallow-layer surface imaging, and imaging resolution is low.OCT image is then fault imaging, can check different depth Blood flow information, different skin blood flow depth can be detected as needed.And OCT has higher resolution ratio, axial Resolution ratio is up to 10 μm.Therefore SkBF is detected based on OCT angiographic imaging technologies, research skin burn, wound Recover to have more preferably observation and analytical effect.However the studies above is based on extracorporeal blood flow imaging research, based on internal blood flow Contrast imaging is studied to injury of lungs, and either esophageal injury or diagnosing tumor also have very important significance alimentary canal.

When carrying out optical signal data acquisition, signal cut-in method used is the existing OCT systems based on frequency sweep：Triggering Signal accesses DAQ board triggering ends, clock sampling signal incoming clock signal end, data-signal access data channel A ends.But The anti-tampering property of this connection method and stability are relatively poor.For this problem, the present invention proposes that a kind of automatic switching signal is defeated Enter acquisition method.This method is directed to conventional connection and is respectively connected to two kinds of moulds of clock sampling signal and data-signal using binary channels Formula designs an automatic converting module and carries out free switching processing.When being disturbed using conventional connection external clock signal or not When stablizing, drainage pattern automatically switches to internal double channels acquisition pattern.

Based endoscopic imaging needs to rotate at a high speed, and rotation at a high speed necessarily causes flating, and blood flow imaging need it is stable into As sequence.Solve the problems, such as that this needs overcomes shake generation or compensation campaign error.The present invention proposes a kind of be used in conduit Front end sets sacculus and the method for combining motion compensation, carries out stabilization processing.

The present invention proposes to peep flow imaging system in a kind of be based on, and is devised certainly for signal access and control model Dynamic switching signal connection mode ensures the stabilization of transmission, while takes into account calculating speed.For blood flow imaging, a kind of stabilization is proposed Sacculus processing system.

【The content of the invention】

It is an object of the invention to provide a kind of high speed endoscopic optical coherent flow imaging systems, including coherent source, interfere mould Block, data acquisition module, sample arm, reference arm, optics rotation terminal, sacculus systems stabilisation, blood flow imaging processing and digital shadow As system.

1. Fig. 1 is the schematic diagram of the specific embodiment of the invention

2. Fig. 2 is another schematic diagram of the specific embodiment of the invention

3. Fig. 3 is the schematic diagram of the specific embodiment of the invention one

4. Fig. 4 is the circuit diagram of the specific embodiment of the invention two

5. Fig. 5 is a kind of circuit diagram of the specific embodiment of the invention three

6. Fig. 6 is another circuit diagram of the specific embodiment of the invention four

7. Fig. 7 is another circuit diagram of the specific embodiment of the invention four

8. Fig. 8 is the circuit diagram of the specific embodiment of the invention four

9. Fig. 9 is another circuit diagram of the specific embodiment of the invention five

10. Figure 10 is another circuit diagram of the specific embodiment of the invention five

11. Figure 11 is another circuit diagram of the specific embodiment of the invention five

12. Figure 12 is the schematic diagram of data acquisition 1

13. Figure 13 is a kind of schematic diagram of data acquisition 2

14. Figure 14 is the schematic diagram of data processing 1

15. Figure 15 is the schematic diagram of data processing 2

16. Figure 16 is the schematic diagram of data transmission of the present invention

17. Figure 17 is another schematic diagram of data transmission of the present invention

18. Figure 18 is a kind of structure chart of inventive samples arm

19. Figure 19 is blood flow imaging algorithm structure figure of the present invention

20. Figure 20 is single saccule rock-steady structure figure of the present invention

21. Figure 21 is the double sacculus rock-steady structure figures of the present invention

22. Figure 22 is image system structure chart of the present invention

23. Figure 23 is kinetic control system of the present invention

24. Figure 24 is the structure chart of three-dimensional imaging of the present invention and roaming

To be easy to understand the technical means, the creative features, the aims and the efficiencies achieved by the present invention, with reference to specific Embodiment, the present invention is further explained.

【Specific embodiment】

Specific embodiment one

Referring to Fig. 1, this part is ultrahigh speed endoscopic optical coherent flow imaging system one of which embodiment, including SLD Light source 2 collimates feux rouges 1, fiber coupler 3, reference arm 4, sample arm 5, circulator 6, interferometer 7 and data transmission 11.

Wideband light source generates an optical signal, is divided into two paths of signals by optical splitter, is returned from sample arm 4 and reference arm 5 Two paths of signals pass through interferometer 7 interference effect, pass to data acquisition module 8 and be acquired, pass through OCT angiography algorithms 9 carry out data processing, it is hereby achieved that the B-scan images of blood-stream image feature, then generate blood flow using enface algorithms Data finally by image system 10 interact with operator.Data acquisition module needs special control card to provide herein Sampling clock.

Specific embodiment two

Referring to Fig. 2, this part is ultrahigh speed endoscopic optical coherent flow imaging system another embodiment therein, including Feux rouges 1, high speed swept light source 12, fiber coupler 3, reference arm 4, sample arm 5, interferometer 7, data acquisition module 2（13）, Oct angiographies algorithm 9, image system 10.

Specific embodiment control is as follows：

High speed swept light source 12 provides optical signal and linear frequency clock signal and trigger signal, optical signal are divided by coupler Two paths of signals respectively enters reference arm 4 and sample arm 5, and the signal of return enters interferometer 7 and interfered, into data acquisition module Block 2（13）, data acquisition module 2 receives interference signal and triggering and clock signal, signal application OCT blood vessels after treatment Radiography algorithm 9 can obtain blood distribution image, be interacted finally by image system and operator.

Embodiment one (automatic clock switchover module)

Automatic clock switchover module as shown in Figure 3.The module is by data acquisition module 15, and signal path chA 16, signal leads to Road chB 17, K-clk input 18, A-Trig 19, clock switchover module 20, detector 21, swept light source 22,23 groups of signal source Into.

Reference clocks of the K-clock as data acquisition, system can adaptively selected drainage pattern in both modes, By judging clock performance parameter Jitter, frequency range, signal strength decision is using pattern 1 or pattern 2.In pattern 1 Lower carry out data acquisition, compared to pattern 2.When in mode 1, occur data acquisition it is unstable when, system can self-adapting detecting It is switched under pattern 2, it is ensured that data acquisition is reliable and stable.Solve the problems, such as clock jitter.

Embodiment two (being as the clock signal of acquisition OCT signals in the form of external clock)

As shown in Figure 4, this figure is as the clock signal schematic diagram of acquisition OCT signals, the module in the form of external clock By data acquisition module 15, signal path chA 16, signal path chB 17, K-clk input 18, A-Trig 19, clock switching Module 20, detector 21, swept light source 22, signal source 23 form.

Illustrate that clock switches in embodiment one, clock switchover module is switched to using external clock as OCT signals and adopts Collect clock, be the mode state.The present embodiment specific embodiment controls：Two-way triggering letter is generated by swept light source Number, it is all the way A-Trigger signals, another way is k-trigger signals, and A-Ttrigger signals access data acquisition module touches Input terminal is sent out, k-Ttrigger signals enter external clock input interface.Detector data signal access signal path ChA simultaneously. The signal path A of access is acquired by external clock.

Embodiment three (is gathered K-clock clock signals and OCT signal parallels with constant frequency clock)

As shown in Figure 5, this figure is as the clock signal schematic diagram of acquisition OCT signals, the module in the form of external clock By data acquisition module 15, signal path chA 16, signal path chB 17, K-clk input 18, A-Trig 19, clock switching Module 20, detector 21, swept light source 22, signal source 23 form.

Illustrate that clock switches in embodiment one, clock switchover module is switched to K-clock with constant frequency clock Clock signal is gathered with OCT signal parallels, is the mode state.The present embodiment specific embodiment controls：By sweeping Frequency light source generates two-way trigger signal, is all the way A-Trigger signals, and another way is k-trigger signals, and A-Ttrigger believes Number access data acquisition module triggering input terminal, k-Ttrigger signal entering signal passage B interface.Detector data letter simultaneously Number access signal path ChA.The signal path A and k-trigger of access are acquired by internal clock.

Embodiment five（The switching of pattern 1 and pattern 2 is completed using hardware）

As shown in Fig. 6,7,8, the present embodiment is to complete pattern 1 and the elaboration of the switching of pattern 2 using hardware.The module is adopted by data Collection module 26, signal path chA 16, signal path chB 17, K-clk input 18, A-Trig 19, clock switchover module 20, Detector 21, swept light source 22, signal source 23, S_in shakes judge access 25, and shake judges 24 compositions.

Shake judges：The k-trigger signals that swept light source is sent enter shake judgment module and are judged, and to judging As a result fed back, thus carry out pattern switching.

The specific control mode of the present embodiment is：Swept light source sends two-way trigger signal, is that A-Trigger signals connect all the way Enter the triggering end of data acquisition module, be k-trigger signal incoming clock handover modules all the way, clock switchover module divides three tunnels It is respectively connected to the external clock input terminal of data acquisition module, signal path ChB ends and shake judgment module.Shake judgment module The k-trigger clocks of access are judged, judge that signal feeds back to data acquisition module, data acquisition module is for feedback Signal, selection are k-trigger to be acquired by ChB using internal clock or using external clock passage to k-trigger It is acquired.

Embodiment six（Pattern switching is completed using algorithm）

As shown in Fig. 9,10,11, the present embodiment is to complete pattern 1 and the elaboration of the switching of pattern 2 using algorithm.The module is by data Acquisition module 26, signal path chA 16, signal path chB 17, K-clk input 18, A-Trig 19, clock switchover module 20, detector 21, swept light source 22, signal source 23,27 composition of S_out outputs.

The specific control mode of the present embodiment is：Swept light source sends two-way trigger signal, is that A-Trigger signals connect all the way Enter the triggering end of data acquisition module, be k-trigger signal incoming clock handover modules all the way, clock switchover module divides two-way It is respectively connected to the external clock input terminal of data acquisition module and signal path ChB ends.Utilize S_cout passages and algorithm acquisition k- Trigger module by signal, assesses the clock performance parameter Jitter of current demand signal clock, frequency range, and signal strength judges to believe Data acquisition module number is fed back to, data acquisition module is directed to feedback signal, and selection is to k- using internal clock by ChB Trigger is acquired or k-trigger is acquired using external clock passage.

Embodiment seven (data acquisition 1)

Data acquisition module as shown in figure 12.The module is by high speed swept light source 2, linear clock k-trigger30, A- Trigger 31, interference light signal 32, photoelectric detector 33, automatic switching module, capture card 34, memory 35, data processing mould Block 1（37）.

When carrying out data signal acquisition, generally require three tunnel signal paths, trigger signal, clock signal sum number it is believed that Number.Under normal conditions, trigger signal is connected with the triggering input terminal of analog input card, and the clock of clock signal and analog input card is defeated Enter end connection, and data-signal is connected (if binary channels) with data channel A or B.Because being to use external clock, This connection mode stability is not especially good, may be malfunctioned under strong interference environment.Another connection mode：Triggering letter Number it is connected with the triggering input terminal of analog input card, clock signal is connected with analog input card data channel A, and data-signal sum number It is connected according to passage B.This mode is acquired the clock signal of A channel using internal clocking, relatively upper a kind of more stable, But, it is necessary to carry out weight to what B was gathered with the clock signal that A channel gathers after needing the clock signal acquisition to input channel A Sampling processing, so operand can be increased.The present embodiment proposes a kind of system for automatically switching two kinds of connection modes, which can Real-time two ways switching is carried out to be directed to environment and hardware.Normal operation acquiescence is first worked using A connection modes, is switched Module sets an automatic detecting circuit, and the tigger signals of detection are detected, then can be automatic if any exception or saltus step It is switched to B connection operating modes.

Linear clock k-trigger and A-trigger are provided by high speed swept light source.Linear clock k-trigger When referring to that clock signal corresponds to acquisition signal, the signal of acquisition is all integer wave number.

Photodetector：Interference light signal needs to be converted into electric signal by photoelectric conversion module, to be sticked by acquisition Row signal data acquisition.

Automatic switching module：Equipped with detecting circuit, signal branch link block, order feedback module.Detecting circuit is to defeated The trigger signals entered are detected, and the connection of signal branch is divided into two paths of signals for trigger signals and accesses board all the way Input terminal is triggered, accesses signal input part all the way.Order feedback, for detecting circuit to detection skip signal sending mode switching Instruction.

Capture card：Using high-speed data acquisition card, data collecting card can provide single channel or multi-channel data acquisition, and adopt With support high speed external clock type collection card.

Memory：The data of acquisition are passed to memory by data collecting card, and memory here refers to memory on board or processing Device memory.Memory on board refers to acceleration processing card memory on board.

Data processing module 1：Subsequent processing is carried out to the data that memory is passed to, will be explained in detail in embodiments below It states.

Specific embodiment is：High speed swept light source 11 exports linear clock k-trigger and A-trigger signals, does Optical signal is related to by photoelectric detector, optical signal is changed into electric signal, linear clock k-trigger, A-trigger sum number it is believed that Number common access capture card.Wherein clock signal, while access triggering input terminal and signal input part.Detecting circuit provides feedback Instruction, switches over for drainage pattern.Capture card gathers signal data and incoming memory.Data processing module 1 is read from memory Access is according to progress data processing.

Embodiment eight (data acquisition module 2)

Data acquisition module 2 as shown in Figure 13.The part includes interference light signal 32, high-speed CCD 38, and control card 39 is adopted Truck 34, memory 35, data processing module 2.

High-speed CCD:High-speed CCD uses frequency-adjustable section camera, and CCD frequencies can reach 150KHZ.

Control card：Control card can be generated control signal and be provided camera a-trigger controls using output signal card.Together When provide capture card start pulse signal, be supplied to capture card trigger signal synchronous with camera trigger signal.

Data processing module 2：Signal resampling by the way of software calibration to acquisition, carries out next number of modules afterwards According to processing.It is calibrated using software, refers to be demarcated first with interference envelope, the data of calibration carry out the signal of acquisition Resampling.

Specific embodiment controls：Interference light signal enters high-speed CCD, and CCD generation triggerings trigger enters control Card, control card generates synchronous triggering signal by the trigger signal of input, all the way into high-speed CCD, all the way into capture card.It is high The data that fast CCD is obtained are transported to capture card.The data that capture card obtains are transmitted to memory, memory transmission be memory on board everywhere It can also be passed directly to processor memory to manage device memory.Data processing module 2 is obtained from memory from data and progress subsequently Reason.

Embodiment nine (data processing 1)

4 are please referred to Fig.1, this part describes a kind of way of example of data transmission, including：Internal storage data 35, data solution It adjusts, accelerator card processing 46, image reconstruction 44, threshold value and color conversion 45.Wherein accelerator card processing includes windowing process 41 again, FFT transform 42, power spectrum asks for 43.

The present embodiment carries out two kinds of data processing modes of A or B for imaging data, and B-mode adds in data demodulation step.

Data demodulation：In TCP data segment, the both of which of automatic switchover is mentioned.When being switched to B-mode, data are led to Road A and data channel B are respectively acquired clock signal and data-signal, therefore need the data to acquisition using this pattern Again demodulated.Demodulation method then uses, and clock signal carries out resampling to data-signal.

Windowing process：When carrying out Fourier transformation, the signal of no line length is intercepted, so causing spectral leakage can be to Picture strip carrys out shot noise.By the way of signal adding window, the image of signal side lobe can be inhibited, energy is made to be relatively concentrated in master Valve just can more really reduce spectrum information.Hanning window or Hamming window may be employed in adding window mode.

FFT transform：Data after adding window are carried out with Fourier transformation, Fourier transformation is used accelerates library function based on figure Carry out computing.The Fourier transformation of spectrum is equal to the auto-correlation of light amplitude, is reflection optical coherence tomography depth information The factor as long as carrying out Fourier transformation to the photoelectric conversion signal of acquisition, takes amplitude information and phase information.Amplitude information can be with B-frame images are indirectly displayed as, phase information may be used as asking for angiography use.

Power spectrum is asked for：Data are converted to obtain power spectrum data using 10 times of logarithmic forms are taken.

Image reconstruction：Image conversion is carried out to the power spectrum data after asking for.Continuous envelope data is split, it is raw Into the data matrix block of single-frame images, then by asking for coordinate transform, polar coordinate image is switched to rectangular co-ordinate image.As Scan image is inside peeped, the data of scanning should be consistent with the shape of blood vessel or enteron aisle alimentary canal iso-cross-section.Present system Scanning is peeped to be interior, so its section is circular diagram.The footpath picture of circular diagram, represents scan depths information.Circular diagram tangentially represents rotation Turn scanning direction.

When carrying out coordinate transform, necessarily cause pixel distribution uneven when due to rectangular pixels matrix conversion being circular diagram It is even, it is sparse close to edge difference pixel distribution, it to carry out improving image quality by way of interpolation.Interpolation method can be used double Cubic interpolation or the tangential interpolation of circle.

Threshold value and color conversion：Threshold value is set, and is set rational gray threshold parameter according to image display effect, is adjusted figure The contrast of picture and lightness variation.Color conversion, provides several pseudo-colours schemes, and gradation of image domain space is gone to color domain Visual effect is improved in space.

The method of the present embodiment may be controlled to：Internal storage data passes to acceleration processing card and is handled, and is accelerating processing card Interior progress windowing process and FFT transform, then ask for power spectrum.Host computer progress image is passed to after getting power spectrum data It rebuilds, then adjusts image threshold and color conversion.

Embodiment ten（Data processing 2）

5 are please referred to Fig.1, the present embodiment is another realization method of data transmission.Including：Interfere envelope data 46, mark Determine algorithm 47, internal storage data 35, linear wave number data 48, accelerator card processing 49, image reconstruction 50, threshold value and color conversion 51.

Interfere envelope data：Sample arm and reference arm return to the signal of coming, the envelope number formed after interferometer is interfered According to.

Calibration algorithm：Clock sampling signal is the signal according to constant duration, and swept light source is that frequency wavelength is continuous The envelope signal of conversion.If directly acquisition is not integer wavelength it will cause the signal of acquisition.It so needs to clock signal A conversion is carried out, becomes that the clock signal of integer wavelength can be gathered.Then using signal after conversion to directly gathering Signal carries out resampling.The method of wave numbers interval timer is converted to etc. by constant duration clock can use Hilbert transform side Method can also be with looking into wave number method.

Linear wave number data：Resampling acquisition is carried out to the data-signal directly gathered using transformed linear clock Data.

Accelerator card processing：The data of acquisition are carried out to accelerate calculating and processing, calculating is accelerated to accelerate parallel using equipment end The processing method based on cuda may be employed in processing method.

The present embodiment may be controlled to：Interference envelope data is demarcated with calibration algorithm, obtains linear wave number clock Signal.The signal data directly gathered enters memory, and then carrying out resampling by linear wave number clock obtains linear wave number data, Linear wave number data enter accelerator card and handle to obtain that treated that data to be imaged carry out image reconstruction, then carry out threshold value and color Coloured silk conversion.

Embodiment 11（Data transmission 1）

6 are please referred to Fig.1, the present embodiment is a kind of implementation of data transfer mode.Including：Photodetection data 52, acquisition Card memory on board 53, association's processing card 54, PC memory 55, human-computer interaction 56.It is specifically described as down：

Photodetection data：Interference envelope carries out the electrical signal data switched to after photoelectric conversion module.

Capture card memory on board：The data of capture card acquisition are in first time incoming memory on board, and memory on board is with counting According to buffering area.

Association's processing card：Association's processing card accelerates to calculate as bottom to be used, and the data of capture card memory on board are passed to association's processing Card carries out big data quantity algorithm computing.

PC memory：Application layer industrial personal computer memory.

Human-computer interaction：Upper computer software control system is used for carrying out data display and user is interactive.

The present embodiment may be controlled to：The acquired input capture card memory on board of photodetector data, memory on board Data enter association's processing card and carry out the acceleration computing of big data quantity algorithm.Data enter PC memory after computing, are then passed to man-machine friendship Mutual software control system.

Embodiment 12（Data transmission 2）

7 are please referred to Fig.1, the present invention is the another embodiment of data transmission.Including：Photodetection data 52 gather snap-gauge Carry memory 53, PC memory 55, accelerator card memory 57, human-computer interaction 58.Wherein module detailed configuration is as follows：

Photodetector data：With embodiment five.

Capture card memory on board：With embodiment five.

PC memory：With embodiment five.

Accelerator card memory：Accelerator card accelerates computing card using figure, and signified memory refers to that setting graphics acceleration card sets herein Standby end memory.

Human-computer interaction：With embodiment five.

The present embodiment specific embodiment is as follows：

For the acquired card acquisition of photodetection data into memory on board, memory on board data enter PC memory, PC memory and acceleration There are one the processes of data exchange, the i.e. data at PC memory end between card memory to be passed to accelerator card memory and be handled, and handles PC memory end is passed to by accelerator card memory again after complete.The data at last PC memory end enter human-computer interaction.

Embodiment 13（Sample arm）

8 are please referred to Fig.1, this part is a kind of embodiment of sample arm.Including：Optics rotation motor 59, endoscopic optical Conduit 60, single saccule systems stabilisation 61.

Optics rotation motor：Mechanical moving parts can be realized and rotate and pull back at a high speed, load conduit and realize complete move Make.

Endoscopic optical conduit：Human body, the equipment diagnosed can be entered.

Single saccule systems stabilisation：Using single balloon design pattern, pop one's head in sacculus Front-end Design.It can make conduit and interior Wall keeps relative stability, the relatively stable image of acquisition when carrying out data acquisition, to realize that blood flow algorithm calculates.

Double sacculus systems stabilisations：Using two balloon design patterns, probe is designed between two sacculus.It can make conduit It keeps relative stability with inner wall, the relatively stable image of acquisition when carrying out data acquisition, to realize that blood flow algorithm calculates.

Embodiment is as follows：

At conduit head end prism, single saccule systems stabilisation or double sacculus systems stabilisations are integrated.Optics rotation motor loads conduit Carry out rotation retractable gathered data.Optics rotation motor integrated optics slip ring, stepper motor and brushless motor.Simultaneously in certain bits Put integrated limiter.When gathering and preserving data, optics rotation motor carries out high speed rotation and the action cooperation image system that pulls back System carries out data acquisition and storage.Since conduit is progress high speed rotation in vivo, balloon system is with respect to there are one in-vivo tissues The power of support, it is possible thereby to ensure stablizing relatively for conduit relative organization, and then the picture frame gathered can also keep relatively steady It is fixed.

Embodiment 14（Motion compensation）

This part is for a kind of movement compensating algorithm of high-velocity scanning endoscopic optical coherent flow imaging system.In embodiment ten In one, balloon design has been carried out for catheter probe, tissue and probe movement thus can be kept opposing stationary.But in practical operation Since conduit rotates, it is possible to cause tissue with respect to the movement of conduit axial direction.This part movement compensating algorithm includes：Image is pre- Processing, image pixel statistics, deviation calculate, motion compensation.

The present embodiment specific embodiment controls：The image preprocessing signal of acquisition carries out arithmetic center and carries out pixel system Then meter carries out deviation calculating according to pixel distribution feature between every frame, deviation computational methods are asked for using interframe variance, passed through Location between frames move iteration, ask for minimum variance.Finally using motion compensation process, kinematic error between every frame is subtracted.As a result, Can preferably it be reduced because the mobile dislocation brought is so as to cause blurred image situation by motion compensation process.

Embodiment 15（Blood flow imaging algorithm）

9 are please referred to Fig.1, this part is a kind of embodiment of blood flow imaging algorithm.Including：Internal storage data 35, calibration are calculated Method resampling 62, spectra calculation 43, generation consecutive image 63, blood flow imaging algorithm parameter setting 64, blood flow algorithm process 65, Enface Processing Algorithms 66, blood-stream image 67, data 68 after sampling, power initial data 69, image data 70.It is specifically described as Under：

Calibration algorithm resampling：Resampling is carried out to the data based on non-linear wave number clock acquisition, in example IV It mentions.

Generate consecutive image：Before blood flow algorithm data is asked for, it is necessary in complete continuous image data.These numbers According to should be that there is over or comprising more than 5 frames image datas on each position.

Blood flow imaging algorithm parameter is set：It needs respectively to institutional framework image, blood-stream image and normalization blood-stream image Threshold range be configured.For the image data that is obtained by resampling, it is necessary to set calibrating parameters.

Blood flow radiography algorithm process：OCT microangiography algorithms are a kind of novel vascular imaging algorithms.Radiography is not required in it Agent, imaging resolution are high, it is non-invasive the features such as there is extensive prospect in medical application.The basic principle of radiography algorithm：Because Skin or other tissue sites are static, and blood flow is movement.So according to the difference between consecutive frame by subtracting each other Mode, obtain that blood flow information can be obtained.Algorithm is specifically described as：In same station acquisition 5-8 frame image datas, every frame Image data includes amplitude component A and phase component ω.OCT angiography algorithms, can be only with based on amplitude component difference Method Δ A asks for blood flow information or is asked for blood flow information Δ A+ Δ ω modes with based on amplitude and two species diversity of phase and asked for Blood flow information.It is only applicable in amplitude difference and calculates the method for blood distribution information to requiring relatively low not require phase in acquisition Stability, it is relatively easy in processing time complexity.And the side of blood distribution information is asked for based on amplitude and phase difference Rule can be more preferable in the effect that axis information and blood vessel connectedness reach.Specifically used method can use as needed.

Enface processing：Rectangle volume data is spliced into all flow characteristic information B-frame data that are calculated, so The blood distribution information being distributed afterwards using most strong projection algorithm.

Blood-stream image：The blood distribution image acquired by enface algorithms.

Image data：Signified image data refers to obtain great amount of images in scanning range and in each position herein Put the scan data of 5 or more.

Algorithm channel：Internal storage data is connected with calibration algorithm resampling, and calibration algorithm resampling is connected with spectra calculation, Spectra calculation and generation successive frame calculate connection, generate consecutive image and blood flow imaging algorithm parameter and set connection, blood flow into It is connected as algorithm parameter sets to connect with blood flow radiography algorithm process, blood flow radiography algorithm process and enface processing connections, Enface processing is connected with blood-stream image.Parallel data channel therewith simultaneously, data connection after internal storage data and sampling, sampling Data are connected with power initial data afterwards, and power initial data is connected with image data, and image data is connected with blood-stream image.

Specific embodiment is as follows：Data after internal storage data is sampled after calibration algorithm resampling, number after sampling Power initial data is obtained according to by spectra calculation.Power initial data obtains continuous through generating successive frame computational algorithm Image data.Then flow characteristic is calculated to consecutive image data using the blood flow imaging algorithm obtained, then further utilized Enface algorithms ask for blood distribution feature.

Embodiment 16（Foley's tube systems stabilisation）

Figure 20 and 21 are referred to, the present invention provides a kind of sacculus OCT image conduit, sacculus is arranged to single saccule system or double Balloon system.Illustrate including figure label：Interface end 71 into geat 72, into note pipe 73, is imaged inner tube 74, sacculus outer tube 75 expands Dehisce 76, maincenter pipe 77, probe 78.Maincenter pipe with interface end, is managed, sacculus outer tube respectively into note, is imaged inner tube, extension mouth phase Even.Interface end connects OCT equipment.Have into note pipe end into geat, for the injection of cleaning solution and contrast agent.Sacculus outer tube front end Equipped with sacculus, which is made of the good material of translucency.Sacculus outer tube is imaging inner tube, is imaged inside inner tube front end Equipped with imaging probe, pop one's head in and be in balloon interior always in scanning process.Extension mouth connects external device (ED), for injecting physiology Brine or air realize the expansion of sacculus.

Advantage：Dilating sacculus can make the position of OCT probe and detection position keep relative stability, human body when avoiding detection Image caused by the minute movement of tissue obscures, and substantially increases image quality, obtains the clear figure for accurately reflecting lesion situation Picture is conducive to diagnosis of the doctor to disease.

Embodiment 17（Image system）

Figure 21 is referred to, this part describes a kind of embodiment of image system.It is pre- including data input 80, image Look at, 81 Image Acquisition 82, B-frame image displays 83, blood-stream image show 84, feature recognition 85, three-dimensional imaging with roaming 86, Repeated acquisition 87.

Feature recognition：The lesion information in image is identified using intelligent recognition algorithm, and lesion type is sorted out, Such as：The focus characteristics such as calcification, fibrosis.

Three-dimensional imaging and roaming：Three-dimensional reconstruction, and the pipeline feature based on scanning are carried out to peeping data in acquisition, is utilized Roaming is peeped in virtual to carry out checking tube chamber internal structure.

The present embodiment step connection mode is：Start to connect with data input, data input is connected with image preview, image Preview is connected with Image Acquisition, and Image Acquisition is connected with B-frame image displays, and B-frame image displays are shown with blood-stream image Show, feature recognition, three-dimensional imaging with roaming connect, blood-stream image show, feature recognition, three-dimensional imaging with roaming with whether repeating Acquisition connection, if repeated acquisition and data input connection.

The present embodiment specific embodiment controls：

Data are inputted into Installed System Memory, then carry out image preview, observe imaging effect.It clicks on image system and starts acquisition Function preserves image.Image after having preserved carries out playback and shows.Next, into promoting circulation of blood on the basis of b-frame Stream picture is shown, feature recognition and three-dimensional imaging and roaming.It can be no with repetitive cycling whole flow process if necessary to repeated acquisition card Then terminate gatherer process.

Embodiment 18（Kinetic control system）

Figure 22 is referred to, this part is a kind of embodiment of kinetic control system.Including：PC89, instruction set 90, movement Control card 91, optical motion control 92, optics rotation motor control 93, tapered end control 94, Polarization Control 95.

Light path motion control：The motor for adjusting optical path length is controlled.

Optics rotation motor controls：Electric rotating machine and motor of pulling back to rotation motor carry out motion control.Control rotation Speed, distance of pulling back, start-stop time.

Tapered end controls：The opening and closing of tapered end are controlled, when conduit is inserted into rotation motor interface, inlay sense inside tapered end Detector notice tapered end is answered to be automatically locked to prevent rotation motor conduit when high speed rotates from dropping out, when equipment gather terminate or Tapered end automatically opens when sending dismounting conduit instruction, for facilitating the dismounting of conduit.

Polarization Control：The rotation of optical fiber can have an impact optical polarization, to control fiber spinning motor controlled from And carry out Polarization Control.

Specifically control is the present embodiment：Order is sent from PC machine and forms instruction set, and instruction set is transmitted to motion control card, fortune Dynamic control card sends order to light path motion control, the control of optics rotation motor, tapered end control, Polarization Control.And these are controlled Module is sent to host computer further through /V feedback, forms the command control system of a closed loop.The tapered end that this implementation is set is certainly Dynamic locking function, can prevent possible Automatic-falling when conduit rotates, the promotion of optical system rotational stabilization is played compared with Good effect.

Embodiment 19（Three-dimensional imaging and roaming architecture）

Figure 23 is referred to, this part is a kind of embodiment of the three-dimensional imaging and roaming architecture for image system, including： FFT power spectrum datas information 96, frame data 97 after coordinate transform, extraction catheter center position 98, VTK data import 99, equivalence Face extraction 100, inner cavity surface render 104, n data center point sets（n>1 natural number）101, spatial axis 105, attribute setup 102, interactive setup 103, IGSTK 106 inside peeps roaming 107.It is described in detail below：

Extract catheter center position：The visual angle of virtual roaming is using the position of conduit axis as visual angle starting point.Extract conduit Central point, i.e., center location in each frame view.

VTK data import：Cake diagram data after coordinate transform is imported into the algoritic module built with VTK, carried out pre- Processing.

Isosurface extraction：Inside peep roaming realized by passage of inner cavity, the contour surface for extracting inner cavity of pipe be into The premise that row three-dimensional is swum slowly.In VTK data lead-in portions, three-dimensional reconstruction has been done to continuous image sequence.This part is to three-dimensional Intracoelomic cavity is rebuild, does an isosurface extraction.And the contour surface information of extraction is stored in memory.

Inner cavity surface renders：It the contour surface information finished has been extracted, does a face using VTK and renders, obtain in complete Cavity surface passage.

N data center point sets：To continuous hundreds of data, all center position coordinates are extracted.

Spatial axis：The axis of all picture centre point set compositions.Axis is fitted by central point and obtained, and approximating method is adopted With cubic spline interpolation to ensure the smooth of axis.

Inside peep roaming：The visual angle of simulated endoscope is constructed from tube chamber interior examination lumen wall.

Attribute setup：Color attribute, transparency property, contrast properties, window width, window bit attribute are done to inner cavity to be rendered Setting.

Interactive setup：To mouse event, KeyEvent is set with the interactive mode for rendering body.

IGSTK：Can virtual roaming function be developed by IGSTK storehouses, be grasped using the progressive mode of coordinate axial coordinate Make.

The specific embodiment of the present embodiment is as follows：

After FFT power spectrum datas information carries out coordinate transform, continuous frame data are obtained.To these continuous frame data extraction conduits Center obtains N（N generally takes 300 ~ 500）Thus data center's point set can ask for spatial axis data.Same time-varying Frame after changing carries out VTK data importings, then calculates isosurface extraction, does inner cavity surface and render.What is obtained renders body, carries out attribute Setting and interactive setup.The inner cavity surface set is rendered using IGSTK storehouses and spatial axis peeped in integrated treatment realization Roaming.

The basic principles, main features and the advantages of the invention have been shown and described above.The technology of the industry Personnel are it should be appreciated that the present invention is not limited to the above embodiments, and the above embodiments and description only describe this The principle of invention, without departing from the spirit and scope of the present invention, various changes and modifications of the present invention are possible, these changes Change and improvement all fall within the protetion scope of the claimed invention.The claimed scope of the invention by appended claims and its Equivalent thereof.

Claims

1. a kind of high speed endoscopic optical coherent flow imaging system, it is characterised in that：The system comprises：

(1) red laser；(2) light source；(3) interferometer；(4) reference arm and sample arm；（5）Sacculus systems stabilisation (6) movement is mended Repay algorithm；(7) automatic clock switchover module；（8）Data acquisition and transport module (9) fiber coupler；(10) optics rotation horse It reaches；(11) host computer image processing system；Optical signal is divided into two-way, is all the way reference arm all the way into sample arm；And reference The light that arm and sample arm return, is passed to interferometer；Host computer image processing system, for carrying out image imaging to the data of acquisition Displaying carries out angiography algorithm process and obtains blood flow imaging data, and 3D is imaged and is peeped in virtual roaming and shows, carries out man-machine friendship Mutually and show.

2. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The data acquisition And transport module, it is initialized including hardware harvester, drainage pattern is set, and hardware layer to internal storage data, which transmits, to be connected.

3. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Described is used at a high speed The light source of endoscopic optical coherent flow imaging system can be that swept light source can also be SLD wideband light sources.

4. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Described is used at a high speed The sample arm of endoscopic optical coherent flow imaging system including control optics rotation terminal, has sacculus systems stabilisation Inside peep scanning conduit.

5. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Optical-electric module and probe The intermediary that module is connected, can transmit optical signalling can simultaneously provide machinery rotation and promote, function of pulling back.

6. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Described is used at a high speed The host computer image processing system of endoscopic optical coherent flow imaging system, wherein involved angiography is made based on OCT Shadow algorithm.

7. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Described is used for data Hop in acquisition and transport module, wherein the memory that is passed to refers to that the data of acquisition are passed to acquisition and processing card Memory on board and GPU accelerator cards memory and calculator processor memory.

8. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Described is used at a high speed The optics rotation terminal of endoscopic optical coherent flow imaging system, wherein mechanical function support two kinds of apparatus works of high definition and overlength Pattern, can free switching.

9. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 3, it is characterised in that：Described is used at a high speed The SLD light sources or swept light source of endoscopic optical coherent flow imaging system, wherein the swept light source is can to provide line Property clock and trigger high speed swept light source, be using narrowband coherent source, SLD light sources are broadband coherent sources.

10. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The reference arm Have the function of to be adjusted automatically, sacculus systems stabilisation is designed in the probe segment of sample arm.

11. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The movement is mended Repay algorithm；Based on image information analysis, using the pixel difference of interframe, movement warp is calculated, from there through movement compensating algorithm Reach registration, to improve blood flow imaging arithmetic accuracy.

12. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The data are adopted Collection and transport module；It carries out signal conversion to interference signal and gathers to be input to memory.

13. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The optics rotation Turn terminal；The intermediary that optical-electric module is connected with probe module, can transmit optical signalling can simultaneously provide machinery rotation and promote, and return Draw function.

14. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The host computer Image processing system is used to carry out the data of acquisition image imaging displaying, carries out angiography algorithm process and obtains blood flow imaging Data carry out human-computer interaction and displaying.

15. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：The host computer Image processing system；Optical signal is divided into two-way, is all the way reference arm all the way into sample arm；And reference arm and sample arm are returned The light returned.

16. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Reference arm is included certainly Dynamic light path regulating system, sample arm include control optics rotation motor, there is the interior of sacculus systems stabilisation to peep scanning conduit.

17. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Automatic clock switching Module section refers to that being utilized respectively hardware automatically switches to automatically switch to switch over selection to acquisition clock with algorithm.

18. according to a kind of high speed endoscopic optical coherent flow imaging system of claim 1, it is characterised in that：Described is passed to Memory refers to that the data of acquisition are passed to acquisition and processing card memory on board and GPU accelerator cards memory and calculator processor memory； The automatic switchover refers to, according to different use environments and using hardware case, automatically select suitable access signal and lead to Road, access module are divided into mode A and B-mode.