CN106343957A - Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof - Google Patents

Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof Download PDF

Info

Publication number
CN106343957A
CN106343957A CN201610816227.2A CN201610816227A CN106343957A CN 106343957 A CN106343957 A CN 106343957A CN 201610816227 A CN201610816227 A CN 201610816227A CN 106343957 A CN106343957 A CN 106343957A
Authority
CN
China
Prior art keywords
unit
processing unit
signal processing
interface unit
picture frame
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
CN201610816227.2A
Other languages
Chinese (zh)
Inventor
朱锐
曹挥
曹一挥
沈诚亮
刘海平
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shenzhen Vivolight Medical Device Technology Co Ltd
Original Assignee
Shenzhen Vivolight Medical Device Technology Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Shenzhen Vivolight Medical Device Technology Co Ltd filed Critical Shenzhen Vivolight Medical Device Technology Co Ltd
Priority to CN201610816227.2A priority Critical patent/CN106343957A/en
Priority to CN201720058984.8U priority patent/CN207286036U/en
Priority to CN201710036413.9A priority patent/CN106580239B/en
Publication of CN106343957A publication Critical patent/CN106343957A/en
Pending legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/04—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances
    • A61B1/05—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances characterised by the image sensor, e.g. camera, being in the distal end portion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00002—Operational features of endoscopes
    • A61B1/00004—Operational features of endoscopes characterised by electronic signal processing
    • A61B1/00009—Operational features of endoscopes characterised by electronic signal processing of image signals during a use of endoscope
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00193—Optical arrangements adapted for stereoscopic vision
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6867—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive specially adapted to be attached or implanted in a specific body part
    • A61B5/6876—Blood vessel
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis

Abstract

The invention provides a three dimensional OCT scan imaging system for cardiovascular applications and an imaging method thereof. The system comprises a detection unit, a probe interface unit, a light signal processing unit, a digital signal processing unit and a display which are connected in sequence; wherein the detection unit includes a optical fiber probe which send the collected sample signal to the light signal processing unit through the probe interface unit; the light signal processing unit is used to process the sample signal to obtain the picture frame; the digital signal processing unit includes a digital data converter, a data calibrator and a feedback controller; the data calibrator is used to conduct the data calibration of the picture frame converted by the data converter one by one and subsequently conduct the three dimensional resegmentation to obtain the three dimensional image. The feedback controller is used to control the moving condition of the probe interface unit based on the lightness information and the gradient information of the picture frame converted by the converter. The three dimensional OCT scan imaging system and the imaging method can increase the precision of the three dimensional OCT images.

Description

It is applied to cardiovascular three-dimensional oct scanning imaging system and its imaging method
Technical field
The present invention relates to cardiovascular based endoscopic imaging technical field, more particularly, to one kind are applied to cardiovascular three-dimensional oct sweeping Retouch imaging system and its imaging method.
Background technology
Optical coherence tomography (optical coherence tomography, oct) technology, is that last decade is sent out rapidly A kind of imaging technique that exhibition is got up, it utilizes the ultimate principle of weak coherent light interferometer, and the light that light source is sent is divided into two bundles, A branch of be transmitted into tested tissue, be also sample arm, another bundle is transmitted into reference to illuminator, is also reference arm, then from tested Tissue and from the two-beam Signal averaging returned with reference to mirror reflection, interference, finally according to optical signal with tested tissue not Show together the gradation of images of different powers, thus being imaged in tissue.
Oct can be divided into time domain oct and frequency domain oct two big class according to know-why.Frequency domain oct has high-resolution due to it Rate, image taking speed are fast, non-invasively organize the advantages such as interior imaging, have been widely used in the organs such as ophthalmology, digestive tract, cardiovascular Imaging.Comparatively speaking, cardiovascular oct system is the most complicated, and the cardiovascular oct equipment of complete set needs to integrate: light source, light splitting Device, optical interdferometer, reference arm, probe interface unit (probe interface unit, piu), conduit, blood flushing liquor note The resources such as injection device, fibre-optical probe, high speed data acquisition system, signal processor, image processing software.Cardiovascular oct is scanned into The ultimate principle of picture is: by piu high-speed rotation and pullback motion, and drives the fibre-optical probe of front end in blood vessel by bourdon tube Inside do Tomography.3d cardiovascular oct has huge potential advantages compared with 2d oct, and 3d cardiovascular oct can be directly perceived For doctor provide blood vessel space three-dimensional structure information, doctor can be helped to be better understood from the spatial shape of thrombosis, support Adherent situation, assess bifurcated lesions, instruct support after expand, instruct thrombectomby etc..
But, 3d cardiovascular oct is absolutely not simply to be stacked to 2d oct sequence image to be rendered to 3d picture together, Because so can there is error in reconstruct, the serious understanding that also can mislead doctor.In real work, due to bourdon tube and conduit Between frictional force can shake in high-speed rotation, lead to actual acquisition to three-dimensional oct image can be axially formed rotation Dislocation, if so directly carrying out three-dimensionalreconstruction to sequence image, is to there is dislocation in three dimensions, therefore, such The meeting that result is inaccurate, serious for clinical analysiss leads to the diagnostic result of mistake.
Content of the invention
In order to solve the above problems, the present invention propose one kind be applied to cardiovascular three-dimensional oct scanning imaging system and its Imaging method, it is possible to increase the degree of accuracy of the oct image of three-dimensional that described three-dimensional oct scanning imaging system obtains.
Concrete technical scheme proposed by the present invention is: provide one kind to be applied to cardiovascular three-dimensional oct scanning imaging system, Described it is applied to the probe unit, probe interface unit, light letter that cardiovascular three-dimensional oct scanning imaging system includes being sequentially connected Number processing unit, digital signal processing unit and display；Described probe unit includes fibre-optical probe, and described fibre-optical probe is used for Action according to described probe interface unit gathers the sample signal of blood vessel, and described sample signal is passed through described probe interface Unit is sent to described optical signal processing unit；Described optical signal processing unit obtains for carrying out process to described sample signal Picture frame；Described digital signal processing unit includes data converter data corrector；Described data corrector is used for respectively Data correction is carried out and three-dimensionalreconstruction obtains 3-D view to the picture frame after the conversion of described data converter, and exports to described Display is shown.
Further, described data corrector includes reference points detection unit, image correction unit and three-dimensionalreconstruction unit； Described reference points detection unit is used for obtaining the position mark point of the picture frame after described data converter is changed, described image school Positive unit obtains school for carrying out rotation transformation according to described position mark point to the picture frame after the conversion of described data converter Picture frame after standard, described three-dimensionalreconstruction unit obtains graphics for carrying out three-dimensionalreconstruction to the picture frame after described calibration Picture.
Further, described digital signal processing unit also includes feedback controller, and described feedback controller is used for basis The monochrome information of picture frame after described data converter conversion and the motion shape of the gradient information described probe interface unit of control State；Described feedback controller includes starting module of pulling back；Described starting module of pulling back is used for detecting whether vessel lumen rinses dry Only and control described probe interface unit starting pullback motion when described vessel lumen is rinsed well.
Further, described starting module of pulling back includes computing unit, judging unit and pulls back and begin to respond to unit, described Computing unit is used for calculating the equal of brightness in predetermined flushing detection zone for the picture frame after described data converter is changed Value and variance；Described judging unit is used for judging whether described average and described variance meet trigger condition, and is meeting triggering Send back during condition and pull open beginning trigger；Described pulling back begins to respond to unit for according to described beginning trigger control of pulling back Make described probe interface unit starting pullback motion.
Further, described feedback controller includes stopping modular of pulling back, and described stopping modular of pulling back is used for detecting described Whether fibre-optical probe moves to precalculated position and controls when described fibre-optical probe moves to described precalculated position described probe to connect Mouth unit stops pullback motion.
Present invention also offers one kind is applied to cardiovascular three-dimensional oct scan imaging method, methods described includes following Step:
Fibre-optical probe gathers the sample signal of blood vessel according to the action of probe interface unit and passes through described sample signal Described probe interface unit is sent to optical signal processing unit；
Optical signal processing unit carries out process and obtains picture frame and described image frame is sent to number to described sample signal Word signal processing unit；
Digital signal processing unit carries out Data correction respectively to described image frame and three-dimensionalreconstruction obtains 3-D view；
Display receives and shows described 3-D view.
Further, described digital signal processing unit carries out Data correction respectively to described image frame and three-dimensionalreconstruction obtains Specifically include to 3-D view step:
Calculate gray value in pre-set radius region for the described image frame, gray threshold and the maximum point of gray value will be met Position mark point as described image frame；
Picture frame after rotation transformation is corrected is carried out according to described position mark point to described image frame；
Three-dimensionalreconstruction is carried out to the picture frame after described correction and obtains 3-D view.
Further, the rotation transformation public affairs that rotation transformation is adopted are carried out according to described position mark point to described image frame Formula is:
[ x y 1 ] = [ x 0 y 0 1 ] c o s θ - s i n θ 0 sin θ c o s θ 0 0 0 1
Wherein, (x0, y0) for described image frame pixel coordinate, (x, y) be described correction after picture frame pixel The coordinate of point, θ represents the anglec of rotation.
Further, described digital signal processing unit carries out Data correction respectively to described image frame and three-dimensionalreconstruction obtains Also include described digital signal processing unit to 3-D view step according to the monochrome information of described image frame and gradient information control Make the kinestate of described probe interface unit；It is preset with first threshold and Second Threshold in described digital signal processing unit, Described digital signal processing unit controls described probe interface unit according to the monochrome information of described image frame and gradient information Kinestate step specifically includes:
Calculate average and the variance of brightness in predetermined flushing detection zone for the described image frame；
Judge whether whether described average be less than described Second Threshold less than described first threshold and described variance, if described Average is less than described first threshold and described variance is less than described Second Threshold, then control described probe interface unit starting to pull back Motion.
Further, it is preset with the 3rd threshold value, the 4th threshold value and the 5th threshold value in described digital signal processing unit, if institute State average and be not less than described first threshold or described variance not less than described Second Threshold, then described digital signal processing unit root Monochrome information and gradient information according to described image frame control the kinestate step of described probe interface unit also to include:
Described image frame is converted to the picture frame under polar coordinate system；
Calculate picture frame under the described polar coordinate system maximum brightness value of every string image radially and greatest gradient value；
Calculate the average of all of maximum brightness value and the average of all of greatest gradient value and variance；
Judge the average of described maximum brightness value whether more than described 3rd threshold value, described greatest gradient value average whether Whether it is less than described 5th threshold value more than the variance of described 4th threshold value and described greatest gradient value, if described maximum brightness value Average is more than the side of described 4th threshold value and described greatest gradient value more than the average of described 3rd threshold value, described greatest gradient value Difference is less than described 5th threshold value, then control described probe interface unit to stop pullback motion.
Proposed by the present invention be applied to cardiovascular three-dimensional oct scanning imaging system and its imaging method have following excellent Point:
(1) it is applied to cardiovascular three-dimensional oct scanning imaging system described in and includes data corrector, data corrector can Respectively Data correction is carried out to the picture frame after data converter conversion and three-dimensionalreconstruction obtains 3-D view；
(2) it is applied to cardiovascular three-dimensional oct scanning imaging system described in and includes feedback controller, it can control described The kinestate of probe interface unit；Described feedback controller includes starting module of pulling back, and starting module of pulling back can detect blood Whether pipe tube chamber is rinsed well and controls described probe interface unit starting to pull back fortune in the case that vessel lumen is rinsed well Dynamic；
(3) described feedback controller also includes stopping modular of pulling back, and described stopping modular of pulling back can detect described optical fiber Whether probe moves to the position of described transparent outer sleeve and moves to the position of described transparent outer sleeve in described fibre-optical probe When control described probe interface unit to stop pullback motion.
Brief description
By combining the following description that accompanying drawing is carried out, above and other aspect of embodiments of the invention, feature and advantage Will become clearer from, in accompanying drawing:
Fig. 1 is the structural representation being applied to cardiovascular three-dimensional oct scanning imaging system；
Fig. 2 is the structural representation of feedback controller in Fig. 1；
Fig. 3 is the structural representation of starting module of pulling back in Fig. 2；
Fig. 4 is the schematic diagram rinsing detection zone；
Fig. 5 is the structural representation of stopping modular of pulling back in Fig. 2；
Fig. 6 is coordinate transform schematic diagram；
Fig. 7 is the structural representation of data corrector in Fig. 1；
Fig. 8 is the process schematic being corrected according to position mark point；
Fig. 9 is the three-dimensionalreconstruction interface schematic diagram in the present embodiment；
Figure 10 is to be applied to cardiovascular three-dimensional oct scan imaging method schematic flow sheet.
Specific embodiment
Hereinafter, with reference to the accompanying drawings to describing embodiments of the invention in detail.However, it is possible to come real in many different forms Apply the present invention, and the present invention should not be construed as limited to the specific embodiment that illustrates here.On the contrary, these enforcements are provided Example is to explain the principle of the present invention and its practical application, so that others skilled in the art are it will be appreciated that the present invention Various embodiments and be suitable for the various modifications of specific intended application.
With reference to Fig. 1, what the present embodiment provided is applied to cardiovascular three-dimensional oct scanning imaging system, for obtaining three-dimensional Oct image, wherein, three-dimensional oct image is made up of multiple images frame.Three-dimensional oct scanning imaging system includes being sequentially connected Probe unit 1, probe interface unit 2, optical signal processing unit 3, digital signal processing unit 4 and display 5.Probe unit 1 includes fibre-optical probe 11, and fibre-optical probe 11 is used for gathering the sample signal of blood vessel and by sample according to the action of probe interface unit 2 Product signal is sent to optical signal processing unit 3 by probe interface unit 2, and the action of probe interface unit 2 here includes rotating With pull back, the sample signal of blood vessel includes blood vessel wall and endovascular signal.Optical signal processing unit 3 is used for sample signal is entered Row process obtains picture frame.Specifically, digital signal processing unit 4 includes feedback controller 41, data corrector 42 data Transducer 44, feedback controller 41 controls for the brightness value according to the picture frame after data converter 44 conversion and Grad to be visited The kinestate of head interface unit 2, here the kinestate of probe interface unit 2 include starting pullback motion and stopping and pull back fortune Dynamic two states, data corrector 42 is used for carrying out Data correction and three-dimensional to the picture frame after data converter 44 conversion respectively Reconstruct obtains 3-D view, and display 5 is used for 3-D view is shown.Three-dimensional oct image is by multiple images frame interpolation Mapping is constituted, the oct image of the three-dimensional after display display mapping.
Probe unit 1 also includes conduit 12, optical fiber 13, transparent outer sleeve 14 and bourdon tube 15, optical fiber 13, bourdon tube 15 and Fibre-optical probe 11 is located in conduit 12.Conduit 12 is connected with probe interface unit 2, and conduit 12 includes internal portion and external body, body Inside is for inserting in internal blood vessel.Flushing liquor inlet 12a is provided with external body, internal portion is away from one end of external body It is additionally provided with flushing liquor outlet 12b, flushing liquor is injected into conduit 12 simultaneously by flushing liquor injection device from flushing liquor inlet 12a Discharge from flushing liquor outlet 12b.Fibre-optical probe 11 is located at internal portion one end away from external body, and it passes through optical fiber 13 and probe Interface unit 2 connects, and bourdon tube 15 is sheathed on optical fiber 13, and transparent outer sleeve 14 is coated in internal portion and is located at fibre-optical probe Between 11 and external body.
Probe interface unit 2 includes motor (not shown), and motor is connected with bourdon tube 15, and motor is used for driving spring pipe 15 Rotation and Return spring pipe 15, bourdon tube 15 occur elastic deformation be tightly sheathed on optical fiber 13 and by optical fiber 13 between Frictional force drives optical fiber 13 to rotate together with fibre-optical probe 11 and pull back optical fiber 13 and fibre-optical probe 11, so that fibre-optical probe 11 In the motion of conduit 12 internal coiling, form spiral three-dimensional scanning.
Optical signal processing unit 3 includes light source 31, beam splitter 32, detector 33, interferometer 34 and illuminator 35.Light source 31 The light beam sending is divided into the duplicate light of two bundles after beam splitter 32 effect, and light beam is transmitted into illuminator by interferometer 34 35, referred to as reference arm, a branch of probe interface unit 2 is sent to by interferometer 34, this light beam is passed through by probe interface unit 2 again Optical fiber 13 transmits and is concurrently incident upon internal blood vessel to fibre-optical probe 11 and is detected, referred to as sample arm.Light in reference arm is through reflective The reference light being formed after mirror 35 reflection incides interferometer 34, is formed after the light menses inside pipe wall reflection in sample arm and scattering Sample signal is received by fibre-optical probe 11 and is back to interferometer 34.Interferometer 34 is overlapped to reference signal and sample signal Produce the optical signal after optical interference is interfered, wherein, different tissue profile forms the light letter after the interference of different powers Number, the power of optical signal can reflect endovascular construction featuress.Detector 33 is used for the optical signal after detection is interfered and by its turn It is changed to the corresponding signal of telecommunication.
Digital signal processing unit 4 also includes data acquisition unit 43.Data acquisition unit 43 is connected with detector 33, and it is used for Receive the described signal of telecommunication and the described signal of telecommunication is converted to the corresponding digital signal of picture frame, data converter 44 is used for receiving institute State digital signal and described digital signal is converted to cartesian coordinate space from polar coordinate space.Wherein, in the present embodiment Data converter 44 can realization in many different forms, including but not limited to processor (cpu), graphic process unit (gpu), Device or their combination in any such as programmable gate array (fpga), microprocessor (as arm), digital signal processor (dsp).
When oct is imaged, generally requires and vessel inner blood is rinsed, otherwise blood has stronger absorption and dissipates to light Penetrate effect, affect image quality.Before triggering cardiovascular oct scanning, clinician's injecting blood flushing liquor, and observe oct As preview screen, when confirming that blood is rinsed well, triggering piu instruction of pulling back manually carries out three-dimensional imaging.However, artificial trigger Piu pulls back and brings very big inconvenience to clinical practice operation, and the too early often vessel inner blood of triggering of pulling back is not rinsed well, causes Image quality is deteriorated it is impossible to meet clinical diagnosises demand；On the contrary, pull back triggering too late, will be to the excessive blood of patient injection Flushing liquor, brings unnecessary side effect to patient.
Additionally, existing cardiovascular oct is often by the distance of pulling back of one fixation of setting, that is, a spacing of pulling back at present Pull back from rear piu triggering stopping.However, when fibre-optical probe withdraws in entrance transparent outer sleeve, the data that it collects is no Effect, the data in transparent outer sleeve, bring the unnecessary wasting of resources not only to Data Post, data storage, After three-dimensional rendering, also can cause to judge by accident to diagnosis.
With reference to Fig. 2, the feedback controller 41 in the present embodiment includes pull back starting module 410 and stopping modular 411 of pulling back. Starting module of pulling back 410 is used for detecting whether vessel lumen is rinsed well and control when vessel lumen is rinsed well probe to connect Mouth unit 2 starts pullback motion, and after probe interface unit 2 starts pullback motion, motor starts to pull back and driving spring pipe is pulled back Optical fiber 13 and fibre-optical probe 11, fibre-optical probe 11 starts screw in conduit 12 and starts three-dimensional spiral scanning.Pull back and stop Only module 411 is used for whether detection fiber probe 11 moves to the position of transparent outer sleeve 14 and move in fibre-optical probe 11 Probe interface unit 2 is controlled to stop pullback motion during the position of transparent outer sleeve 14, probe interface unit 2 stops pullback motion Afterwards, motor stops the rotation and stops driving spring pipe 15, and now, fibre-optical probe 11 stops scanning.
Specifically, with reference to Fig. 3, Fig. 4, starting module of pulling back 410 includes the first computing unit 100, the first judging unit 101 And pull back and begin to respond to unit 102, for the ease of distinguishing, here the computing unit pulled back in starting module is named as the first meter Calculate unit 100, the judging unit pulled back in starting module is named as the first judging unit 101.First computing unit 100 is used for Calculate the brightness i of the digital signal in the cartesian coordinate space in predetermined flushing detection zone1Average and variance, It is preset with first threshold th in one judging unit 1011And Second Threshold th2, the first judging unit 101 is used for judging described average Whether it is less than first threshold th1And whether described variance is less than Second Threshold th2And it is less than first threshold th in described average1And Described variance is less than Second Threshold th2When send back and pull open beginning trigger and give back to pull open beginning response unit 102, pull back and start to ring Answer unit 102 for according to pull back beginning trigger control probe interface unit 2 startup pullback motion, i.e. described average and institute State variance and meet following trigger condition:
mean(i1) ＜ th1
std(i1) ＜ th2.
In the present embodiment by the width setup of predetermined flushing detection zone be conduit diameter 2 times (as shown in Figure 4), when So, predetermined flushing detection zone can determine according to practical situation, does not limit here.If vessel lumen is rinsed well, Then the average of the brightness of detection zone of annular and variance should be less, therefore, when described average and described variance meet above two During individual condition, the first judging unit 101 produces one and pulls back and starts trigger and send described beginning trigger of pulling back Give back to pull open beginning response unit 102, the motor beginning to respond in unit 102 control probe interface unit 2 of pulling back starts to revolve at a high speed Turn and drive bourdon tube 15 to rotate, bourdon tube 15 occurs elastic deformation and drives optical fiber 13 by the frictional force between optical fiber 13 Rotate with fibre-optical probe 11 and pull back optical fiber 13 and fibre-optical probe 11, so that fibre-optical probe 11 moves in conduit 12 internal coiling, Form spiral three-dimensional scanning, finally obtain endovascular three-dimensional spiral scanogram.
With reference to Fig. 5, Fig. 6, stopping modular 411 of pulling back includes the second computing unit 103, the second judging unit 104 and pulls back Stop response unit 105.Second computing unit 103 is used for being converted to the digital signal in the cartesian coordinate space in Fig. 6 Digital signal in polar coordinate space (ρ, θ), wherein, ρ is polar diameter, and θ is polar angle.Second computing unit 103 is additionally operable to calculate pole Maximum brightness value i on digital signal in coordinate space every string radiallydAnd greatest gradient value g and calculate all of Big brightness value idAverage and the average of all of greatest gradient value g and variance.
It is preset with the 3rd threshold value th in second judging unit 1043, the 4th threshold value th4And the 5th threshold value th5, second judges list Unit 104 is used for judging maximum brightness value idAverage whether be more than the 3rd threshold value th3, whether the average of greatest gradient value g more than the Four threshold values th4And whether the variance of greatest gradient value is less than the 5th threshold value th5And in maximum brightness value idAverage be more than the 3rd threshold Value th3, greatest gradient value g average be more than the 4th threshold value th4And the variance of greatest gradient value g is less than the 5th threshold value th5When send Stopping trigger of pulling back gives back to draw stopping response unit 105, and stopping response unit 105 of pulling back controls in probe interface unit 2 Motor stop pulling back fibre-optical probe 11, i.e. maximum brightness value idAverage, the average of greatest gradient value g and greatest gradient value g Variance meet following three conditions:
mean(id) ＞ th3
Mean (g) ＞ th4.
Std (g) ＜ th5
Wherein, by using the prewitt boundary filter sensitive to vertical edge to the numeral letter in polar coordinate space Number processed, obtain gradient image, then detect greatest gradient value g on every string radially, then calculate all of The gradient mean value of big Grad g and variance.When maximum brightness value idAverage, the average of greatest gradient value g and greatest gradient value g Variance meet simultaneously above three formulas when, then illustrate that this image frame in includes transparent outer sleeve 14, i.e. fibre-optical probe 11 Move to predetermined position.
With reference to Fig. 7, Fig. 8, in order to improve the degree of accuracy of the oct image of three-dimensional, the data corrector 42 in the present embodiment Including reference points detection unit 420, image correction unit 421 and three-dimensionalreconstruction unit 422.Reference points detection unit 420 is used for Obtain the position mark point of the digital signal in cartesian coordinate space, its flute in pre-set radius region especially by detection The gray value of the digital signal in karr coordinate space, meets gray threshold if there are multiple points, then take maximum gradation value institute right The location point answered is as the labelling point of the digital signal in cartesian coordinate space.
Image correction unit 421 is used for carrying out school according to position mark point to the digital signal in cartesian coordinate space The picture frame after calibration will definitely be arrived, it carries out school especially by rotational transformation matrix to the digital signal in cartesian coordinate space Standard, the rotation transformation that the present embodiment is adopted is rotated based on picture centre, and the matrix of rotation transformation is:
h = c o s θ - s i n θ 0 sin θ c o s θ 0 0 0 1
Rotation transformation formula is as follows:
[ x y 1 ] = [ x 0 y 0 1 ] c o s θ - s i n θ 0 sin θ c o s θ 0 0 0 1
In formula, (x0, y0) for original coordinate system coordinate, (x, y) is the coordinate of pixel in postrotational picture frame, θ table Show the anglec of rotation, just clockwise turn to, rotate counterclockwise is negative.As shown in figure 8, after calibration, all images in sequence The labelling point of frame is longitudinally being based on identical direction.
Three-dimensionalreconstruction unit 422 obtains 3-D view for carrying out three-dimensionalreconstruction to the picture frame after calibration, and it specifically will Picture frame after calibration passes through three-dimensionalreconstruction algorithm, that is, according to color mapping and opacity mapping function, by the figure after calibration As frame is mapped to projected image plane by object plotting method.
With reference to Fig. 9, Fig. 9 shows the three-dimensionalreconstruction interface according to the present embodiment.It comprises cardiovascular 3d to show Show window, longitudinal cross-section display window, lateral cross section display window and control panel.By the present embodiment it can be seen that right After Cardiovascular data calibration, its three dimensional structure can accurately reflect out blood vessel and each assembly of Ink vessel transfusing (as conduit, seal wire) Actual position.
With reference to Figure 10, the present embodiment additionally provides a kind of oct scan imaging method, for obtaining the oct image of three-dimensional, three The oct image of dimension is made up of multiple images frame, the method comprising the steps of:
Step s1, fibre-optical probe 11 gather the sample signal of blood vessel according to the action of probe interface unit 2 and believe sample Number optical signal processing unit 3 is sent to by probe interface unit 2.
Wherein, step s1 specifically includes first under the guiding of seal wire and x light radiography, by PCI Fibre-optical probe 11 is inserted position to be scanned, then flushing is injected in flushing liquor inlet 12a by flushing liquor injection device Liquid is rinsed to the blood in vessel lumen, and meanwhile, fibre-optical probe 11 collection sample signal simultaneously will by probe interface unit 2 Sample signal is sent to optical signal processing unit 3.
Step s2, optical signal processing unit 3 carry out process and obtain picture frame and picture frame is sent to number to sample signal Word signal processing unit 4.
Step s3, digital signal processing unit 4 carry out Data correction respectively to picture frame and three-dimensionalreconstruction obtains graphics Picture.
Step s4, display 5 receive and show 3-D view.
Specifically, in step s3, digital signal processing unit 4 carries out Data correction respectively to picture frame and three-dimensionalreconstruction obtains Comprise the following steps to 3-D view:
Calculate gray value in pre-set radius region for the described image frame, gray threshold and the maximum point of gray value will be met Position mark point as described image frame；
Picture frame after rotation transformation is corrected is carried out according to described position mark point to described image frame；
Three-dimensionalreconstruction is carried out to the picture frame after described correction and obtains 3-D view.
Specifically, step s3 also includes digital signal processing unit 4 according to the monochrome information of picture frame and gradient information control The kinestate of probe interface unit 2 processed；Wherein, it is preset with first threshold and Second Threshold in digital signal processing unit 4, number Word signal processing unit 4 controls the kinestate of probe interface unit 2 to include according to the monochrome information of picture frame and gradient information Following steps:
Calculate brightness i in predetermined flushing detection zone for the described image frame1Average and variance；
Judge whether described average is less than first threshold th1And whether described variance is less than Second Threshold th2If, described equal Value is less than first threshold th1And described variance is less than Second Threshold th2, then probe interface unit 2 is controlled to start pullback motion.
If described average is not less than first threshold th1Or described variance is not less than Second Threshold th2, then step s3 also include:
Described image frame is converted to the picture frame under polar coordinate system；
Calculate maximum brightness value i of picture frame under described polar coordinate system every string image radiallydAnd greatest gradient Value g；
Calculate all of maximum brightness value idAverage and the average of all of greatest gradient value g and variance；
Judge maximum brightness value idAverage whether be more than the 3rd threshold value th3, whether the average of greatest gradient value g more than the Four threshold values th4And whether the variance of greatest gradient value g is less than the 5th threshold value th5If, maximum brightness value idAverage be more than the 3rd threshold Value th3, greatest gradient value g average be more than the 4th threshold value th4And the variance of greatest gradient value g is less than the 5th threshold value th5, then control Probe interface unit 2 processed stops pullback motion.
The present embodiment propose be applied to cardiovascular three-dimensional oct scanning imaging system and its imaging method have following excellent Point:
(1) it is applied to cardiovascular three-dimensional oct scanning imaging system and includes data corrector 42, data corrector 42 can Respectively Data correction is carried out to the picture frame after data converter 44 conversion and three-dimensionalreconstruction obtains 3-D view, improve three-dimensional Oct image degree of accuracy；
(2) it is applied to cardiovascular three-dimensional oct scanning imaging system and includes feedback controller 41, it can control probe to connect The kinestate of mouth unit 2；Feedback controller 41 includes starting module 410 of pulling back, and starting module of pulling back 410 can detect blood vessel Whether tube chamber is rinsed well and controls probe interface unit 2 to start pullback motion in the case that vessel lumen is rinsed well；
(3) feedback controller 41 also includes stopping modular 411 of pulling back, and stopping modular 411 of pulling back being capable of detection fiber probe 11 positions whether moving to transparent outer sleeve 14 simultaneously control spy when fibre-optical probe 11 moves to the position of transparent outer sleeve 14 Head interface unit 2 stops pullback motion.
Although illustrate and describing the present invention with reference to specific embodiment, it should be appreciated by those skilled in the art that: In the case of without departing from the spirit and scope of the present invention being limited by claim and its equivalent, can here carry out form and Various change in details.

Claims (10)

1. one kind is applied to cardiovascular three-dimensional oct scanning imaging system it is characterised in that described be applied to cardiovascular three-dimensional At probe unit that oct scanning imaging system includes being sequentially connected, probe interface unit, optical signal processing unit, digital signal Reason unit and display；Described probe unit includes fibre-optical probe, and described fibre-optical probe is used for according to described probe interface unit Action gather the sample signal of blood vessel, and described sample signal is sent to described optical signal by described probe interface unit Processing unit；Described optical signal processing unit obtains picture frame for carrying out process to described sample signal；Described digital signal Processing unit includes data converter data corrector；Described data corrector is used for respectively described data converter being changed Picture frame afterwards carries out Data correction and three-dimensionalreconstruction obtains 3-D view, and exports and shown to described display.
2. according to claim 1 it is applied to cardiovascular three-dimensional oct scanning imaging system it is characterised in that described number Include reference points detection unit, image correction unit and three-dimensionalreconstruction unit according to corrector；Described reference points detection unit is used for Obtain the position mark point of the picture frame after described data converter conversion, described image correction unit is used for according to described position Labelling point carries out the picture frame after rotation transformation is calibrated, described Three-dimensional Gravity to the picture frame after the conversion of described data converter Structure unit obtains 3-D view for carrying out three-dimensionalreconstruction to the picture frame after described calibration.
3. according to claim 1 it is applied to cardiovascular three-dimensional oct scanning imaging system it is characterised in that described number Word signal processing unit also includes feedback controller, and described feedback controller is used for the figure after changing according to described data converter As the monochrome information of frame and the kinestate of the gradient information described probe interface unit of control；Described feedback controller includes pulling back Starting module；Described starting module of pulling back is used for detecting whether vessel lumen is rinsed well and rinsed in described vessel lumen dry Control described probe interface unit starting pullback motion when net.
4. according to claim 3 it is applied to cardiovascular three-dimensional oct scanning imaging system it is characterised in that described time Starting module is drawn to include computing unit, judging unit and pull back and begin to respond to unit, described computing unit is used for calculating described number Average and variance according to brightness in predetermined flushing detection zone for the picture frame after transducer conversion；Described judging unit is used In judging whether described average and described variance meet trigger condition, and send back when meeting trigger condition and pull open beginning triggering letter Number；Described pulling back begins to respond to unit for controlling described probe interface unit starting to return according to described beginning trigger of pulling back Roping is moved.
5. according to claim 1 it is applied to cardiovascular three-dimensional oct scanning imaging system it is characterised in that described anti- Feedback controller includes stopping modular of pulling back, and described stopping modular of pulling back is used for detecting whether described fibre-optical probe moves to pre-determined bit Put and control when described fibre-optical probe moves to described precalculated position described probe interface unit to stop pullback motion.
6. one kind is applied to cardiovascular three-dimensional oct scan imaging method it is characterised in that the method comprising the steps of:
Fibre-optical probe gathers the sample signal of blood vessel according to the action of probe interface unit and passes through described sample signal described Probe interface unit is sent to optical signal processing unit；
Optical signal processing unit carries out process and obtains picture frame and described image frame is sent to numeral letter to described sample signal Number processing unit；
Digital signal processing unit carries out Data correction respectively to described image frame and three-dimensionalreconstruction obtains 3-D view；
Display receives and shows described 3-D view.
7. according to claim 6 it is applied to cardiovascular three-dimensional oct scan imaging method it is characterised in that described number Word signal processing unit carries out Data correction respectively to described image frame and three-dimensionalreconstruction obtains 3-D view step and specifically includes:
Calculate gray value in pre-set radius region for the described image frame, using meet the maximum point of gray threshold and gray value as The position mark point of described image frame；
Picture frame after rotation transformation is corrected is carried out according to described position mark point to described image frame；
Three-dimensionalreconstruction is carried out to the picture frame after described correction and obtains 3-D view.
8. according to claim 7 it is applied to cardiovascular three-dimensional oct scan imaging method it is characterised in that according to institute The rotation transformation formula that rheme tagging point carries out that to described image frame rotation transformation adopted is:
[ x y 1 ] = [ x 0 y 0 1 ] cos θ - s i n θ 0 s i n θ c o s θ 0 0 0 1
Wherein, (x0, y0) for described image frame pixel coordinate, (x, y) be described correction after picture frame pixel Coordinate, θ represents the anglec of rotation.
9. according to claim 6 it is applied to cardiovascular three-dimensional oct scan imaging method it is characterised in that described number Word signal processing unit carries out Data correction respectively to described image frame and three-dimensionalreconstruction obtains 3-D view step and also includes institute State the monochrome information according to described image frame for the digital signal processing unit and the fortune of the gradient information described probe interface unit of control Dynamic state；It is preset with first threshold and Second Threshold, described digital signal processing unit root in described digital signal processing unit Monochrome information and gradient information according to described image frame control the kinestate step of described probe interface unit to specifically include:
Calculate average and the variance of brightness in predetermined flushing detection zone for the described image frame；
Judge whether whether described average be less than described Second Threshold less than described first threshold and described variance, if described average Less than described first threshold and described variance is less than described Second Threshold, then described probe interface unit starting is controlled to pull back fortune Dynamic.
10. according to claim 9 it is applied to cardiovascular three-dimensional oct scan imaging method it is characterised in that described number It is preset with the 3rd threshold value, the 4th threshold value and the 5th threshold value, if described average is not less than described first threshold in word signal processing unit Value or described variance are not less than described Second Threshold, then described digital signal processing unit is according to the monochrome information of described image frame The kinestate step controlling described probe interface unit with gradient information also includes:
Described image frame is converted to the picture frame under polar coordinate system；
Calculate picture frame under the described polar coordinate system maximum brightness value of every string image radially and greatest gradient value；
Calculate the average of all of maximum brightness value and the average of all of greatest gradient value and variance；
Judge whether whether the average of described maximum brightness value be more than more than described 3rd threshold value, the average of described greatest gradient value Whether the variance of described 4th threshold value and described greatest gradient value is less than described 5th threshold value, if the average of described maximum brightness value It is more than described 4th threshold value more than the average of described 3rd threshold value, described greatest gradient value and the variance of described greatest gradient value is little In described 5th threshold value, then described probe interface unit is controlled to stop pullback motion.
CN201610816227.2A 2016-09-09 2016-09-09 Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof Pending CN106343957A (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
CN201610816227.2A CN106343957A (en) 2016-09-09 2016-09-09 Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof
CN201720058984.8U CN207286036U (en) 2016-09-09 2017-01-17 A kind of angiocarpy three-dimensional optical coherent video system
CN201710036413.9A CN106580239B (en) 2016-09-09 2017-01-17 A kind of angiocarpy three-dimensional optical coherent video system

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN201610816227.2A CN106343957A (en) 2016-09-09 2016-09-09 Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof

Publications (1)

Publication Number Publication Date
CN106343957A true CN106343957A (en) 2017-01-25

Family

ID=57859173

Family Applications (3)

Application Number Title Priority Date Filing Date
CN201610816227.2A Pending CN106343957A (en) 2016-09-09 2016-09-09 Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof
CN201720058984.8U Withdrawn - After Issue CN207286036U (en) 2016-09-09 2017-01-17 A kind of angiocarpy three-dimensional optical coherent video system
CN201710036413.9A Active CN106580239B (en) 2016-09-09 2017-01-17 A kind of angiocarpy three-dimensional optical coherent video system

Family Applications After (2)

Application Number Title Priority Date Filing Date
CN201720058984.8U Withdrawn - After Issue CN207286036U (en) 2016-09-09 2017-01-17 A kind of angiocarpy three-dimensional optical coherent video system
CN201710036413.9A Active CN106580239B (en) 2016-09-09 2017-01-17 A kind of angiocarpy three-dimensional optical coherent video system

Country Status (1)

Country Link
CN (3) CN106343957A (en)

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106846347A (en) * 2017-02-15 2017-06-13 深圳市中科微光医疗器械技术有限公司 Stenter to implant based on OCT preoperative analysis system and analysis method
CN107518877A (en) * 2017-08-25 2017-12-29 广州永士达医疗科技有限责任公司 A kind of calibrating installation and method of OCT conduits
CN107945176A (en) * 2017-12-15 2018-04-20 西安中科微光影像技术有限公司 A kind of colour IVOCT imaging methods
CN108553088A (en) * 2018-05-11 2018-09-21 苏州阿格斯医疗技术有限公司 OCT systems
CN109223047A (en) * 2018-09-19 2019-01-18 深圳开立生物医疗科技股份有限公司 A kind of Ultrasound Instrument

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106343957A (en) * 2016-09-09 2017-01-25 深圳市中科微光医疗器械技术有限公司 Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP5523791B2 (en) * 2008-10-27 2014-06-18 株式会社東芝 X-ray diagnostic apparatus and image processing apparatus
WO2013103342A1 (en) * 2012-01-04 2013-07-11 Draeger Medical Systems, Inc. Patient identification and monitoring system
US9351698B2 (en) * 2013-03-12 2016-05-31 Lightlab Imaging, Inc. Vascular data processing and image registration systems, methods, and apparatuses
US9702762B2 (en) * 2013-03-15 2017-07-11 Lightlab Imaging, Inc. Calibration and image processing devices, methods, and systems
EP3071103A1 (en) * 2013-11-18 2016-09-28 Volcano Corporation Tracking an intraluminal catheter
CN106343957A (en) * 2016-09-09 2017-01-25 深圳市中科微光医疗器械技术有限公司 Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106846347A (en) * 2017-02-15 2017-06-13 深圳市中科微光医疗器械技术有限公司 Stenter to implant based on OCT preoperative analysis system and analysis method
CN107518877A (en) * 2017-08-25 2017-12-29 广州永士达医疗科技有限责任公司 A kind of calibrating installation and method of OCT conduits
WO2019037142A1 (en) * 2017-08-25 2019-02-28 广州永士达医疗科技有限责任公司 Oct conduit calibration apparatus and method
CN107945176A (en) * 2017-12-15 2018-04-20 西安中科微光影像技术有限公司 A kind of colour IVOCT imaging methods
CN107945176B (en) * 2017-12-15 2021-05-11 西安中科微光影像技术有限公司 Color IVOCT imaging method
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
CN109223047A (en) * 2018-09-19 2019-01-18 深圳开立生物医疗科技股份有限公司 A kind of Ultrasound Instrument
CN109223047B (en) * 2018-09-19 2022-04-15 深圳开立生物医疗科技股份有限公司 Ultrasonic instrument

Also Published As

Publication number Publication date
CN207286036U (en) 2018-05-01
CN106580239A (en) 2017-04-26
CN106580239B (en) 2018-12-04

Similar Documents

Publication Publication Date Title
CN106343957A (en) Three dimensional OCT scan imaging system for cardiovascular applications and imaging method thereof
CN103028185B (en) Automatic vessel intervention device, system and method based on real-time volume ultrasonic waves
EP2208467B1 (en) Ultrasound diagnosis apparatus, ultrasound image processing apparatus, image display method, and computer program product
CN101336844B (en) Medical image processing apparatus and medical image diagnosis apparatus
CN108042125B (en) High-speed endoscopic optical coherent blood flow imaging system
JP2014217745A (en) Ultrasonic diagnostic apparatus and method of controlling the same
JP6611880B2 (en) Data display and processing algorithms for 3D imaging systems
BR112015011288B1 (en) Ultrasound diagnostic system for imaging multiple planes of a fetal heart; method for ultrasound imaging a plurality of different selected image planes of a target anatomy, in real time; and method for ultrasound imaging a plurality of different selected image planes of a fetal heart, in real time
WO1999013432A1 (en) Apparatus and method for determining three-dimensional representations of tortuous vessels
CN109498063A (en) A kind of three-dimensional intravascular ultrasound image system and imaging method
CN101170948A (en) Ultrasonographic device and image processing method thereof
JP2010246767A (en) Three-dimensional image construction device and image processing method
JP6717801B2 (en) Image diagnostic apparatus and image construction method
WO2023072146A1 (en) Transluminal ultrasonic automatic inspection system, control method, computer-readable storage medium and electronic device
WO2019164662A1 (en) Thrombus detection during scanning
EP1952359A1 (en) System and method for generating for display two-dimensional echocardiography views from a three-dimensional image
CA2663898A1 (en) Systems and methods for restoring a medical image affected by nonuniform rotational distortion
US10159467B2 (en) Method for seam elimination and reconstruction of coplanar images from intravascular ultrasonic data
JP2022545219A (en) Ultrasonic guidance dynamic mode switching
US8870750B2 (en) Imaging method for medical diagnostics and device operating according to this method
WO2021193007A1 (en) Program, information processing method, information processing device, and model generating method
WO2021065750A1 (en) Diagnosis assistance device, diagnosis assistance system, and diagnosis assistance method
JP5354885B2 (en) Ultrasound diagnostic system
CN113256530A (en) Respiratory tract OCT data processing method and system
CN210055992U (en) Intravascular dual-mode imaging device

Legal Events

Date Code Title Description
C06 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
C02 Deemed withdrawal of patent application after publication (patent law 2001)
WD01 Invention patent application deemed withdrawn after publication

Application publication date: 20170125