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WO2024137352A1 - Synchronisation d'un système de tomographie par cohérence optique - Google Patents

Synchronisation d'un système de tomographie par cohérence optique Download PDF

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Publication number
WO2024137352A1
WO2024137352A1 PCT/US2023/084141 US2023084141W WO2024137352A1 WO 2024137352 A1 WO2024137352 A1 WO 2024137352A1 US 2023084141 W US2023084141 W US 2023084141W WO 2024137352 A1 WO2024137352 A1 WO 2024137352A1
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Prior art keywords
line
straight line
scans
correlation
processor
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English (en)
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Gerald Mcmorrow
Jongtae Yuk
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Veravanti Inc
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Veravanti Inc
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Priority claimed from US18/083,945 external-priority patent/US12385733B2/en
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    • 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

Definitions

  • Chronic Total Occlusion refers to a complete obstruction of the coronary artery.
  • CTOs can result from coronary artery disease and develop due to atherosclerosis. The blockage prevents all downstream blood flow, and can cause a range of symptoms and issues, including chest pain and heart attacks. In some patients, however, CTOs cause no physically identifiable symptoms, e.g., silent heart attacks, and the CTOs go undiagnosed. Many patients with CTO also do not receive therapy due to practical difficulties of penetrating the occlusion with partially complete angiographic images.
  • IVUS Intravascular Ultrasound
  • OCT Optical Coherence Tomography
  • IVUS traditionally utilizes a catheter with an ultrasound probe on a proximal end and provides a cross-sectional view of blood vessels.
  • OCT operates similarly but utilizes the longitudinal partial coherence of light rather than time delay of sound waves, to obtain information from reflected, scattered light.
  • OCT can provide resolution on the order of micrometers, but its penetration depth is often limited to several millimeters below tissue surface.
  • Both IVUS and OCT provide only a radial visualization at the imaging location. This requires the imaging device to pass by the occlusion to image it.
  • Scanning Fiber Endoscopes can provide color imaging based on RGB reflectance, and wide-field viewing of the internal arterial region and proximal CTO. SFE imaging techniques only provide surface information within the artery and of the proximal end of the CTO.
  • the invention herein combines forward looking RGB reflectance images combined with forward penetrating sectional images of CTO using OCT.
  • SFE probes scan at approximately 10 kHz for RGB imaging, which provides a single revolution time of about 100 ps. This rotation leaves little time for any OCT scan. Scanning with OCT while changing the location of the scan this quickly would cause the OCT image to be useless from excessive lateral motion artifact.
  • OCT imagers require 7-8 ps imaging time per line and deliver a 100 kHz A-line acquisition speed. At this rate, during one spiral rotation, only 10 A-line samples can be obtained, thus resulting in poor OCT lateral resolution due to probe movement artifact during the wavelength-sweep and a lack of A-lines to compose the penetrating B-mode image.
  • significant modifications are required to be made, e g., changing the length of fiber inside the SFE, but such changes are often not adequate for RGB imaging, causing slow frame rates and larger rigid length of the RGB imager.
  • Methods for synchronizing an Optical Coherence Tomography (OCT) system including detection when a plurality of A-line scans obtained from reflected light of a cantilever scanning fiber within a probe oscillating along a scanning path that increases in amplitude over time are no longer being obtained at a point along the oscillating scanning path when the scanning fiber reaches a minimum speed, determining a value by which a phase angle of the oscillating scanning path is out of synchronization with the plurality of A-line scans, and adjusting a trigger clock for the obtaining the plurality of A-line scans based on the value.
  • OCT Optical Coherence Tomography
  • the present invention can be applied to various medical applications, including but not limited to scanning and imaging within a blood vessel lumen to identify at least one of an occlusion, a defect within an occlusion, a calcification, adventitia, a microchannel, or other features within a vessel or the body.
  • FIG. 1(a) illustrates a forward looking SFE image with an RGB image of a human finger shown in the inset.
  • FIG. 1(b) illustrates several line scans where, using methods described herein, OCT penetrating image of a cross-sectional “cutaway image” can be displayed.
  • the system herein can scan with a spiral raster scan or can scan with line scans as shown in FIG. 1(b).
  • FIG. 1(c) illustrates a cross-sectional image plane that can be selected electronically relative to the RGB surface image.
  • FIG. 2 illustrates a block diagram of a duplex imager capable of RGB surface images and OCT penetrating images in accordance with embodiments described herein.
  • FIG. 3 illustrates a duplex image system inserted into a lumen 310.
  • Display 320 illustrates duplex imager having RGB surface image and OCT penetrating image of a CTO 330.
  • FIGs. 4(a) and 4(b) illustrate two methods of constructing three- dimensional images from the OCT penetrating image frames, with FIG. 4(a) illustrating a method using acquired planes, and FIG. 4(b) illustrating a method using reconstructed slices.
  • FIGs. 5(a) illustrates a normal, slowly scanned OCT image
  • FIG. 5(b) illustrates a simulated compounding image
  • FIG. 6 illustrates the critical method to scan and acquire the OCT mode penetrating scan, during one frame of normal use for a surface RGB image.
  • FIG. 7 illustrates the synchronization of a spectrometer trigger clock with the driving frequency of an SFE probe.
  • FIG. 8 illustrates a correlation-based synchronization scheme for synchronization using OCT A-mode scans/samples collected while the SFE probe sweeps the object at the edge.
  • FIG. 9 illustrates a correlation plot for Line-to-Line and Neighbor-to- Neighbor correlations.
  • FIG. 10 illustrates a B-mode scan of a flat surface for use in a flat-surface imaging synchronization scheme.
  • FIG. 11 illustrates the relationship between synchronized and unsynchronized B-mode scans related to image focus for an image focus-based synchronization scheme.
  • FIG. 12 is a block diagram illustrating a processing implementation of the various synchronization schemes.
  • FIG. 13 is a block diagram illustrating a scheme for training the Al engine of FIG. 12.
  • FIG. 14 illustrates a relationship between lateral resolution and a radius of a B-mode scan.
  • FIG. 15 illustrates absorption coefficients of tissue constituents for various wavelengths.
  • FIG. 16 illustrates an example computing environment in accordance with embodiments discussed herein.
  • the present disclosure relates to duplex imaging techniques. More particularly, the present disclosure combines high-resolution surface images obtained with SFE, and high-resolution penetrating OCT images obtained through Optical Coherence Tomography (OCT), from a Scanning Fiber Endoscope (SFE), and interleaving frames to improve resolution and identify below surface information of biological structures.
  • OCT Optical Coherence Tomography
  • SFE Scanning Fiber Endoscope
  • SFE high resolution color imaging technology combined with forward-looking OCT, allows visualization of occlusions, and visualization below the surface of the occlusion prior to penetration.
  • micro channels, calcifications, and adventitia can be imaged to provide additional clinical benefits and information.
  • a physician can, for example, identify and more safely penetrate the CTO, using a guidewire or other means, and identify a CTO’s location and strong or weak aspects (calcification or microchannels) prior to penetration.
  • aspects of the invention further provide the ability to acquire three-dimensional (3D) OCT data.
  • combining SFE and interleaved frames of an OCT can provide a forward viewing direction and cross-sectional information of the CTO.
  • the present invention can utilize certain OCT A-line acquisitions to construct frames of compounded B-mode images to identify a subsurface tissue information.
  • FIG. 1(b) for example, identifies possible B-mode scanning angles, as indicated on a Cartesian plane with the straight lines, each input can be represented by a sinusoidal wave, and the phase difference between the inputs control the motion of imaging scans, which are typically linear. Note that OCT images are gathered only when the linear scan reaches the maximum amplitude and minimum velocity, this allows excellent OCT lateral resolution. This slow motion is like the momentary lack of motion when a child’s swing reaches max height and reverses direction.
  • FIG. 1 There are also frames of spiral surface mode scans depicted in FIG. 1. These form a raster scan to scan the surface of the scene in front of it. Note that the surface speed of the scanning is very high and would “smear” the OCT scans, thus the spiral scan is used for OCT only.
  • B-mode scans from various rotational angles, a cone-shaped three-dimensional image can be obtained.
  • the 3D data can be visualized in the form of multiple B-mode images acquired or reconstructed from various directions and angles.
  • FIG. 1(b) illustrates these principles and B-mode scanning angles with respect to a cartesian coordinate plane.
  • the cartesian plane and lines 110, 120, 130 are indicative of the probe’s scanning angle with respect to a top surface of an OCT image.
  • the two inputs X and Y represent an oscillating movement of the probe with respect to the imaging plane.
  • the relationship between X and Y indicates the overall scanning motion, which can result in imaging of a particular area in a potential OCT field of view.
  • FIG.1(a) illustrates a forward looking SFE image of the surfaces of the anatomy facing the imaging SFE catheter.
  • a spiral raster scan may be used to bend the SFE fiber using a cantilever resonance of the fiber stub within the SFE imager.
  • An RGB image of a human finger, as an example of the anatomy that can be imaged, from an actual imager is shown in the inset.
  • two orthogonal sinusoidal waves, X and Y with the same frequency, e.g., sin(27i//) and COS(2TI//), can create a circular motion for imaging if the phase differences of the sinusoidal waves are 90° or 7i/2 radians.
  • the angle is controlled via relative amplitude.
  • the 130a and 110a scans differ only in amplitude, same phase.
  • OCT Penetrating Scan Mode 120a a phase difference of 180° or 71 radians between each input, X and Y, also results in the scanning motion becoming linear, as represented by line 120a in Quadrants II and IV, and corresponding graph 120b.
  • the scanning motion is linear, but in the opposite direction and in opposite Quadrants. Scan angles are controlled by amplitude; the same phase shown is equal amplitudes.
  • FIG.1(c) illustrates one such cross-sectional image plane that can be selected electronically relative to the RGB surface image, with the various scanning angles graphed on a Cartesian plane.
  • the straight lines depict planes of penetrating OCT images that are possible, the spiral depicts the raster scan for the RGB surface image.
  • These two image modalities occur by sharing frames in the 30 frame per second system disclosed herein. In effect one can have the RGB image and several planes of OCT “into the occlusion” images simultaneously. One could have 28 frames of RGB and 2 separate OCT “cutaway” images per second. The resultant user image pair is illustrated in the insets.
  • FIG. 2 illustrates a block diagram of an example duplex imaging system 200 usable with one or more embodiments discussed herein.
  • the diagram illustrates a scanning probe 202, such as an SFE, alternately performing both RGB scans 205 and penetrating B-mode scans 210, along the linear line indicated on the RGB image 220.
  • the B-mode scan 210 along the linear line comprises collecting a plurality of A-mode information obtained at the oscillation endpoints of the scan (See also FIG. 6).
  • the collected information from the B-mode scan may be processed through one or more computing devices (e.g., PC 240), interferometers (e.g., interferometer 250), and spectrometers (e.g., spectrometer 255) to produce the OCT image 230.
  • the RGB scan 205 produces the RGB surface image 220, which is created from RGB reflected light through the collection fiber 214 of the scanning probe 202.
  • the RGB surface image is processed by color separator 223, light detector 224, and digitizer 225 and input to the RGB imager 290.
  • a plurality of OCT images obtained from linear scans taken at various angles at the imaging location can be used to produce, a three-dimensional image, and/or information related to a forward-facing view from the end of the SFE.
  • surface-mode scans may be obtained from a spiral scanning fiber.
  • the scanning probe 202 may comprise an oscillating scanning fiber 211 activated by one or more actuators 212, one or more lenses 213 through which emitted light may be directed and focused, and the collection fiber 214 to receive reflected light for analysis. RGB light is able to propagate through the interferometer unaffected.
  • the collected light may be first analyzed by at least one interferometer 250, which can help identify an origin and location of reflected light.
  • a reference arm 215 may be utilized to provide a reference point for the interferometer 250, and additional components/sy stems such as an RGB laser 270, OCT Broadband Light Source 280, and combiner 260 can further contribute towards the interferometer’s function.
  • interferometer data, and additional spectrometer 255 data may be passed to the computing system 240, which may comprise one or more computing devices to perform additional processing with regard to each obtained OCT image.
  • Processing at PC 240 may comprise a B-mode conversion module 242, Fast Fourier Transforms (FFT) 244, a baseline subtraction module 246 and a dispersion compensation 248. This processing can produce an OCT image 230.
  • FFT Fast Fourier Transforms
  • FIG. 3 illustrates an example imaging operation within a blood vessel which may utilize the B-Mode imaging system 200.
  • FIG. 3 illustrates a side view of a blood vessel lumen 310 containing an occlusion 330, an OCT scanning/imaging area 340, RGB scanned surface 360, and a display 320 of the RGB SFE and OCT scanned area.
  • a scanning probe 350 which may comprise an oscillating scanning fiber as described herein, scans between width 360 to provide a forward-looking view within the blood vessel.
  • this forward view, e.g., along the length of the lumen, of the RGB image 360 and the penetrating view of 340 can allow observation of the surface of an occlusion 385 and a penetrating view of the occlusion 390 prior to or during contact or penetration.
  • the occlusion 330 contains a calcification 370 and a microchannel 380 running through the occlusion. These features may be identified in the display section 320, which illustrates an RGB surface image 385 and a corresponding penetrating OCT image 390 along a scanning line 395a.
  • the OCT image 390 may permit observation of a first view of the occlusion 330 which likely depicts subsurface microchannel 380 as well as the calcification 370.
  • the RGB image 385 permits a surface view of the occlusion 385.
  • RGB images 385 combined with OCT subsurface images 390 are forward-facing and can therefore characterize and guide therapy upon occlusion 330 and other surface and subsurface features, e.g., microchannel 380, within the viewable area in a manner not possible with either image alone.
  • OCT subsurface images are be obtained from a linear scanning motion.
  • Each linear scan produces a fan-shaped OCT image 390, which can provide depth information, and be usable to identify one or more features beyond or within occlusions, blockages, and areas beyond surface-level features.
  • the resulting B-mode image targets comprise a plurality of A- lines orthogonal to the scanning path and typically have a fan shape since the origin of the scanning probe 350 and its light point is a single point oscillating between width 360.
  • the imaging depth in the fan-shaped B-mode can be determined by one or more variables in the OCT scanning scheme, including but not limited to reference arm length, swept-source bandwidth, and wavelength resolution.
  • Multiple linear penetrating OCT scans may be obtained at various angles across the circular RGB image scanning area.
  • the illustrated linear scan line 395a corresponds to the end view of the image plane of OCT image 390.
  • the scans along line 395a produce OCT image 390, which may contain information indicative of the occlusion 330, calcification 370, and microchannel 380.
  • Subsequent linear scans may be obtained at the operator’s command to the software, with each scan line being rotated around a central point in the viewing area 360.
  • FIG. 4(a) illustrates this concept by generating three-dimensional data from a plurality of acquired linear planes. Since each obtained A-line information contains information along the light source path, the image has path-dependency. That is, the images are affected by the reflection of layers on the line of sight, and such data provides information to identify the object structure from the image.
  • the three-dimensional object structure can provide valuable information to a clinician, such as volume of a region. Additionally, a volumetric survey of the CTO can be performed to allow the interventionalist to select the optimum crossing technique.
  • two-dimensional image slices having path-dependency can be reconstructed to acquire the three-dimensional structure.
  • the sliced B-mode images can be obtained from an arbitrary scanning angle from the scan origin. In this way, path-dependency between slices can be preserved.
  • FIGs. 5(a) and Fig. 5(b) illustrate results of the above recursive acquisition simulation.
  • FIG. 5(a) illustrates an original OCT B-mode image, wherein the image is slowly acquired using conventional OCT.
  • FIG. 5(b) is a simulated compounding image reconstructed using recursive data acquisition. The image dithering in FIG. 5(b) is due to the simulated scanner translation during an OCT wavelength-sweep. In both images, the interval between A-lines are a 10-pixel distance.
  • FIG. 6 illustrates a B-mode edge scan and data acquisition scheme.
  • the sinusoidal scanning path 600 represents the area through which a probe and its light source are driven during a linear scan.
  • the speed of the probe is at a maximum along center line 630, and at a minimum (i.e., zero speed) along the edge line 620 (during which A-line acquisition occurs), which has an increasing, linear slope 640.
  • Note the slow scan motion during acquisition i.e., 5 pSec).
  • A-line data is exclusively collected at the endpoints of the B-mode scan, where the fiber scan movement is slowest while it reverses course. In this manner, data can be acquired at the most stable probe position.
  • FIG. 6 illustrates 250 oscillations or spirals, during the OCT B-mode scan 610 resulting in 500 A-line acquisitions along endpoints of the scanning area.
  • the radius is linearly increased as the scan travels along linear slope 640.
  • Graph 650 enlarges a portion of an edge lie scan at a point where the A-line data is collected, and the probe movement is minimal.
  • a conventional spectral domain OCT can take 5ps to take an A-line spectrometer reading 660.
  • the spectrometer trigger clock (typically around 20 kHz) may be synchronized to the driving frequency of the SFE probe (typically around 10 kHz and half that of the trigger clock), along with a phase offset (a delay within a period (e.g., 50 ps)), in order to acquire two A-modes of data per a period of sinusoid at the edge of the B-mode scan.
  • a phase offset a delay within a period (e.g., 50 ps)
  • the SFE probe is typically calibrated in a factory prior to delivery to an end user, but environmental conditions during subsequent use, such as aging or ambient temperature, can affect the driving patten and phase and result in the spectrometer trigger clock no longer being synchronized to the edge of the B-mode scan.
  • there may be at least three schemes for synchronizing the B-mode scan with the spectrometer trigger clock including a correlation-based scheme, a flat-surface imaging scheme, and an image focus-based scheme.
  • the Line-to-Line correlation (L-L correlation) would be between one OCT scan/sample and its nearest neighbors, which would minimize when the A-line triggers are at perfect alignment of the phase angle of the B-mode scan.
  • the Neighbor-to-Neighbor correlation (N-N correlation) would be maximum at the same point, as the two nearest neighbors would be looking at the same target region (assuming no probe motion).
  • a graph 900 of the N-N correlation 910 and L-L correlation 920 is illustrated in FIG. 9.
  • the OCT system may be stabilized for drift, such as by adjusting the offset 710.
  • the surface on the image should be a flat or straight line 1000, as shown on the left side of FIG. 10, provided the B-mode scan is synchronized with the spectrometer trigger at the edge of the B-mode scan.
  • the trigger is off from the edge of the B-mode scan (i .e., either earlier or later), resulting in a negative or positive phase delay, the image span may be reduced by the miss-alignment of the trigger.
  • the resulting image, the non-straight line 0101 on the right side of FIG. 10, will illustrate the amount of phase delay.
  • the image focus-based scheme will now be described.
  • the lateral extent of any feature at a given depth is at a minimum. This is because the fiber angle change (from one end of a line sample to the other end of the line sample) is maximized.
  • the spectrometer trigger is synchronized to the edge of the B- mode scan, the image has optimum focus, which may be illustrated from the image 1100 on the left of FIG. 11. If the trigger is not synchronized to the edge, due the spectrometer exposure time, the spectrometer response is collected while the fiber is move, thereby causing the image to be less focused, as shown by image 1110 on the right side of FIG. 11.
  • lateral Fast Fourier Transforms of captured images at various phase angles around an optimum phase angle may be generated.
  • An Artificial Intelligence (Al) system may then be utilized to analyze the FFTs of the images and identify the image with the optimum phase angle, which information may then be used to synchronize the trigger point, i.e. adjust the phase offset.
  • An Al-based system 1200 may also be utilized to implement each one or all of the other schemes for synchronizing the trigger point as further illustrated in FIG. 12.
  • A-mode lines i.e., samples
  • B-mode image 1220 which are created from the A-line scans
  • L-L correlation processor 1230 and N-N correlation processor 1240 operating in parallel
  • the output of the B-mode image 1220 may in turn be input to a lateral FFT processor 1250 and/or a straight-line processor 1260, each also operating in parallel with the other processors.
  • the output of each of the processors 1230, 1240, 1250 and 1260 may then be input to a previously trained Al engine that analyzes the input date and determines in real-time a phase correction for adjusting the spectrometer trigger.
  • FIG. 13 illustrates an embodiment for generating learning statistics for training the Al engine 1270 of FIG. 12.
  • the SFE OCT scanning trigger clock is around 20 kHz, it is too high to be used in order to acquire A-line images for ground truth image sets.
  • These image sets may then be fed into the Al training engine 1300, along with decision parameters 1330 for each of the spectrometer trigger schemes, to generate learning statistics for training the Al engine 1270.
  • FIG. 13 illustrates an embodiment for generating learning statistics for training the Al engine 1270 of FIG. 12.
  • FIG. 14 illustrates a relationship between motion induced reduction of lateral resolution and the radius of a B-mode scan (defined as the distance between the SFE probe and an imaging surface).
  • the X-axis represents the B-mode scan radius (mm) on the imaging surface and Y-axis represents displacement of the probe during A-line acquisition time.
  • Line 1440 represents the probe’s moving distance during A-line acquisitions at each B-mode radius. For example, using a 5 microsecond acquisition window, at a 2.5 mm depth, the image would move 30 microns laterally.
  • Horizontal lines 1410, 1420, 1430 represent lateral resolution based on a maximum B-mode scan radius. At a depth of 5 mm, represented by 1410, the motion during acquisition would be 20 microns.
  • FIG. 15 illustrates absorption coefficients of tissue constituents, applicable to various embodiments and applications of the B-mode scans and methods discussed herein.
  • the SFE probe transmits single mode laser lights for RGB and OCT imaging through the shared single mode fiber.
  • the wavelengths of RGB are typically between 400-700 nm and OCT is between 900-1300 nm.
  • the appropriate single mode fiber and OCT wavelength should be chosen to transmit both RGB and OCT in single mode without significant loss or mode changes (to multimode).
  • FIG. 15 illustrates that in the 700-1100 nm wavelength range, the average absorption rate of materials is less than 10%, thus being particularly applicable for vascular applications.
  • FIG. 16 illustrates an exemplary computing environment in which embodiments of the present invention is depicted and generally referenced as computing environment 1600.
  • computing system generally refers to a dedicated computing device with processing power and storage memory, which supports operating software that underlies the execution of software, applications, and computer programs thereon.
  • computing environment 1600 includes bus 1610 that directly or indirectly couples the following components: memory 1620, one or more processors 1630, I/O interface 1640, and network interface 1650.
  • Bus 1610 is configured to communicate, transmit, and transfer data, controls, and commands between the various components of computing environment 1600.
  • Computing environment 1600 typically includes a variety of computer-readable media.
  • Computer-readable media can be any available media that is accessible by computing environment 1600 and includes both volatile and nonvolatile media, removable and non-removable media.
  • Computer-readable media may comprise both computer storage media and communication media. Computer storage media does not comprise, and in fact explicitly excludes, signals per se.
  • Computer storage media includes volatile and nonvolatile, removable and non-removable, tangible and non-transient media, implemented in any method or technology for storage of information such as computer-readable instructions, data structures, program modules or other data.
  • Computer storage media includes RAM; ROM; EE-PROM; flash memory or other memory technology; CD-ROMs; DVDs or other optical disk storage; magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices; or other mediums or computer storage devices which can be used to store the desired information, and which can be accessed by computing environment 1600.
  • Communication media typically embodies computer-readable instructions, data structures, program modules or other data in a modulated data signal such as a carrier wave or other transport mechanism and includes any information delivery media.
  • modulated data signal means a signal that has one or more of its characteristics set or changed in such a manner as to encode information in the signal.
  • communication media includes wired media, such as a wired network or direct-wired connection, and wireless media, such as acoustic, RF, infrared and other wireless media. Combinations of any of the above should also be included within the scope of computer-readable media.
  • Memory 1620 includes computer-storage media in the form of volatile and/or nonvolatile memory.
  • the memory may be removable, non-removable, or a combination thereof.
  • Memory 1620 may be implemented using hardware devices such as solid-state memory, hard drives, optical-disc drives, and the like.
  • Computing environment 1600 also includes one or more processors 1630 that read data from various entities such as memory 1620, I/O interface 1640, and network interface 1650.
  • I/O interface 1640 enables computing environment 1600 to communicate with different input devices and output devices.
  • input devices include a keyboard, a pointing device, a touchpad, a touchscreen, a scanner, a microphone, a joystick, and the like.
  • output devices include a display device, an audio device (e.g. speakers), a printer, and the like.
  • processor 1610 is often connected to processor 1610 through a serial port interface that is coupled to the system bus, but may be connected by other interfaces, such as a parallel port, game port, or universal serial bus (USB).
  • a display device can also be connected to the system bus via an interface, such as a video adapter which can be part of, or connected to, a graphics processor unit.
  • I/O interface 1640 is configured to coordinate I/O traffic between memory 1620, the one or more processors 1630, network interface 1650, and any combination of input devices and/or output devices.
  • Network interface 1650 enables computing environment 1600 to exchange data with other computing devices via any suitable network.
  • program modules depicted relative to computing environment 1600, or portions thereof, may be stored in a remote memory storage device accessible via network interface 1650. It will be appreciated that the network connections shown are exemplary and other means of establishing a communications link between the computers may be used.
  • circuitry used through the disclosure can include specialized hardware components.
  • circuitry can include microprocessors configured to perform function(s) by firmware or switches.
  • circuitry can include one or more general purpose processing units and/or multi-core processing units, etc., that can be configured when software instructions that embody logic operable to perform function(s) are loaded into memory, e.g., RAM and/or virtual memory.
  • an implementer may write source code embodying logic and the source code can be compiled into machine readable code that can be processed by the general purpose processing unit(s).
  • ROM EEPROM electrically erasable programmable read-only memory
  • hard disk not shown
  • RAM random access memory
  • removable magnetic disk not shown
  • optical disk not shown
  • cache of processing unit a cache of processing unit
  • program modules may be stored on the hard disk, magnetic disk, optical disk, ROM, EEPROM or RAM, including an operating system, one or more application programs, other program modules and program data. It will be appreciated that the various features and processes described above may be used independently of one another or may be combined in various ways. All possible combinations and sub-combinations are intended to fall within the scope of this disclosure.
  • Conditional language used herein such as, among others, “can,” “could,” “might,” “may,” “e.g.,” and the like, unless specifically stated otherwise, or otherwise understood within the context as used, is generally intended to convey that certain embodiments include, while other embodiments do not include, certain features, elements, and/or steps. Thus, such conditional language is not generally intended to imply that features, elements and/or steps are in any way required for one or more embodiments or that one or more embodiments necessarily include logic for deciding, with or without author input or prompting, whether these features, elements and/or steps are included or are to be performed in any particular embodiment.
  • a method for synchronizing an Optical Coherence Tomography (OCT) system comprising detecting when a plurality of A-line scans obtained from reflected light of a cantilever scanning fiber within a probe oscillating along a scanning path that increases in amplitude over time are no longer being obtained at a point along the oscillating scanning path when the scanning fiber reaches a minimum speed; determining a value by which a phase angle of the oscillating scanning path is out of synchronization with the plurality of A- line scans; and adjusting a trigger clock for the obtaining the plurality of A-line scans based on the value.
  • OCT Optical Coherence Tomography
  • the detecting includes obtaining a series of samples of at least one A-line scan among the plurality of A-lines scans just before, during and after the scanning fiber reaches the minimum speed, generating a Line-to-Line (L-L) correlation between at least one sample among the series of samples and nearest neighbor samples to the at least one sample among the series of samples, and generating a Neighbor-to-Neighbor (N-N) correlation between the at least one sample and two nearest neighbor samples, and wherein determining includes adjusting the value to minimize the L-L correlation and to maximize the N- N correlation.
  • L-L Line-to-Line
  • N-N Neighbor-to-Neighbor
  • the detecting includes inputting the plurality of A-line scans to an L-L processor and to an N-N processor operating in parallel with the L-L processor in order to generate the L-L correlation and the N-N correlation
  • the determining includes outputting the L-L correlation and the N-N correlation to a trained Artificial Intelligence (Al) engine to adjust the value in real-time.
  • Al Artificial Intelligence
  • detecting includes determining if a B-line scan image constructed from the plurality of A-line scans is a straight line or a non-straight line, and wherein when the image is a non-straight line the determining includes further or alternatively adjusting the value until the non-straight line becomes the straight line.
  • the detecting includes inputting the plurality of A-line scans to an L-L processor and to an N-N processor operating in parallel with the L-L processor in order to generate the L-L correlation and the N-N correlation, constructing B-line scan images from a series of the plurality of A-line scans, and outputting the B-line scan images to a processor operating in parallel with the L-L processor and the N-N processor for analyzing whether each image among the B-line scan images is the straight line or the non-straight line, and wherein the determining includes outputting the L-L correlation, the N-N correlation, and a straight/non-straight line determination to a trained Artificial Intelligence (Al) engine to determine how to adjust the value in real-time.
  • Al Artificial Intelligence
  • detecting includes determining if a B-line scan image constructed from the plurality of A-line scans is a straight line or a non-straight line, and wherein when the image is a non-straight line the determining includes adjusting the value until the non-straight line becomes the straight line.
  • the detecting includes constructing B-line scan images from a series of the plurality of A-line scans and outputting the B-line scan images to a processor for analyzing whether each image among the B-line scan images is the straight line or the non-straight line, and wherein the determining includes outputting a straight/non- straight line determination to a trained Artificial Intelligence (Al) engine to adjust the value in real-time.
  • Al Artificial Intelligence
  • detecting includes determining if B-line scan images constructed from the plurality of A-line scans are in focus or out of focus, and wherein when the B-line scan images are out of focus the determining includes adjusting the value until one of the B-line scan images becomes in focus.
  • the determining includes generating Fast Fourier Transforms (FFTs) of a series of B-line scan images when the plurality of A-line scans are at various phase angles around an optimum phase angle, and analyzing the FFTs to determine if the B-line scan images are in focus or out of focus, and wherein the determining includes outputting an in focus/out of focus determination to a trained Artificial Intelligence (Al) engine to adjust the value in real-time.
  • FFTs Fast Fourier Transforms
  • Al Artificial Intelligence
  • the detecting includes obtaining a series of samples of at least one A-line scan among the plurality of A-lines scans just before, during and after the scanning fiber reaches the minimum speed, generating a Line-to-Line (L-L) correlation between at least one sample among the series of samples and nearest neighbor samples to the at least one sample among the series of samples, and generating a Neighbor-to-Neighbor (N-N) correlation between the at least one sample and two nearest neighbor samples, and wherein the determining includes further or alternatively adjusting the value to minimize the L-L correlation and to maximize the N-N correlation.
  • L-L Line-to-Line
  • N-N Neighbor-to-Neighbor
  • detecting includes determining if a B-line scan image constructed from the plurality of A-line scans is a straight line or a non-straight line, and wherein when the image is a non-straight line the determining includes further or alternatively adjusting the value until the non-straight line becomes the straight line.
  • the detecting includes generating Fast Fourier Transforms (FFTs) of a series of B-line scan images when the plurality of A-line scans are at various phase angles around an optimum phase angle, analyzing with a lateral FFT processor the FFTs to determine if the B-line scan images are in focus or out of focus, inputting the plurality of A-line scans to an L-L processor and to an N-N processor operating in parallel with the L-L processor in order to generate the L-L correlation and the N-N correlation, constructing B-line scan images from a series of the plurality of A-line scans; and outputting the B-line scan images to a processor operating in parallel with the L-L processor, the N-N processor and the lateral FFT processor for analyzing whether each image among the B-line scan images is the straight line or the non-straight line, and wherein the determining includes outputting the L-L correlation, the N- N correlation, a straight/non-straight line determination and
  • the detecting includes generating Fast Fourier Transforms (FFTs) of a series of B-line scan images when the plurality of A-line scans are at various phase angles around an optimum phase angle, analyzing with a lateral FFT processor the FFTs to determine if the B-line scan images are in focus or out of focus, and outputting the B- line scan images to a processor operating in parallel with the lateral FFT processor for analyzing whether each image among the B-line scan images is the straight line or the non-straight line, and wherein the determining includes outputting an in focus/out of focus determination and a straight/non-straight line determination to a trained Artificial Intelligence (Al) engine to determine how to adjust the value in real-time.
  • FFTs Fast Fourier Transforms

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Abstract

Procédés de synchronisation d'un système de tomographie par cohérence optique (OCT) comprenant la détection lorsqu'une pluralité de balayages de ligne A obtenus à partir de la lumière réfléchie d'une fibre de balayage en porte-à-faux à l'intérieur d'une sonde oscillant le long d'une trajectoire de balayage qui augmente en amplitude au cours du temps ne sont plus obtenus en un point le long de la trajectoire de balayage oscillante lorsque la fibre de balayage atteint une vitesse minimale, ce qui détermine une valeur par laquelle un angle de phase de la trajectoire de balayage oscillante est désynchronisé de la pluralité de balayages de ligne A, et l'ajustement d'une horloge de déclenchement pour l'obtention de la pluralité de balayages de ligne A sur la base de la valeur.
PCT/US2023/084141 2022-12-19 2023-12-14 Synchronisation d'un système de tomographie par cohérence optique Ceased WO2024137352A1 (fr)

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US18/083,945 2022-12-19
US18/083,945 US12385733B2 (en) 2020-01-30 2022-12-19 Synchronizing an optical coherence tomography system

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CN119791559A (zh) * 2025-01-15 2025-04-11 厦门大学 一种连续实时可调焦距的内窥oct探头

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US20190223714A1 (en) * 2018-01-23 2019-07-25 Amo Wavefront Sciences, Llc Methods and systems of optical coherence tomography with fiducial signal for correcting scanning laser nonlinearity
US20210055543A1 (en) * 2018-03-09 2021-02-25 Scinvivo B.V. Mems mirror for oct probe and method of manufacturing such mems mirror
US20210239451A1 (en) * 2020-01-30 2021-08-05 Veravanti Inc. Forward looking rgb/optical coherence tomography duplex imager

Patent Citations (3)

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Publication number Priority date Publication date Assignee Title
US20190223714A1 (en) * 2018-01-23 2019-07-25 Amo Wavefront Sciences, Llc Methods and systems of optical coherence tomography with fiducial signal for correcting scanning laser nonlinearity
US20210055543A1 (en) * 2018-03-09 2021-02-25 Scinvivo B.V. Mems mirror for oct probe and method of manufacturing such mems mirror
US20210239451A1 (en) * 2020-01-30 2021-08-05 Veravanti Inc. Forward looking rgb/optical coherence tomography duplex imager

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN119791559A (zh) * 2025-01-15 2025-04-11 厦门大学 一种连续实时可调焦距的内窥oct探头

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