EP2568865A1 - Reconstruction de forme rapide de fibres optiques - Google Patents

Reconstruction de forme rapide de fibres optiques

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Publication number
EP2568865A1
EP2568865A1 EP11716306A EP11716306A EP2568865A1 EP 2568865 A1 EP2568865 A1 EP 2568865A1 EP 11716306 A EP11716306 A EP 11716306A EP 11716306 A EP11716306 A EP 11716306A EP 2568865 A1 EP2568865 A1 EP 2568865A1
Authority
EP
European Patent Office
Prior art keywords
optical fiber
shape
fiber
anchor point
segment
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.)
Withdrawn
Application number
EP11716306A
Other languages
German (de)
English (en)
Inventor
Luis Felipe Gutierrez
Raymond Chan
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.)
Koninklijke Philips NV
Original Assignee
Koninklijke Philips Electronics NV
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 Koninklijke Philips Electronics NV filed Critical Koninklijke Philips Electronics NV
Publication of EP2568865A1 publication Critical patent/EP2568865A1/fr
Withdrawn legal-status Critical Current

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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
    • A61B1/00163—Optical arrangements
    • A61B1/00165—Optical arrangements with light-conductive means, e.g. fibre optics
    • A61B1/00167—Details of optical fibre bundles, e.g. shape or fibre distribution
    • 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
    • A61B1/005—Flexible endoscopes
    • A61B1/009—Flexible endoscopes with bending or curvature detection of the insertion part
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
    • A61B5/065—Determining position of the probe employing exclusively positioning means located on or in the probe, e.g. using position sensors arranged on the probe
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/12—Devices for detecting or locating foreign bodies
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B34/00—Computer-aided surgery; Manipulators or robots specially adapted for use in surgery
    • A61B34/20—Surgical navigation systems; Devices for tracking or guiding surgical instruments, e.g. for frameless stereotaxis
    • A61B2034/2046—Tracking techniques
    • A61B2034/2061—Tracking techniques using shape-sensors, e.g. fiber shape sensors with Bragg gratings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0261—Strain gauges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
    • A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
    • A61M25/0133—Tip steering devices

Definitions

  • the present invention generally relates to a shape reconstruction of optical fibers.
  • the present invention specifically relates to a specification of different segments of an optical fiber for shape reconstruction at different temporal rates.
  • Minimally invasive medical procedures are performed by inserting a needle, catheter, tube, endoscope or other medical device percutaneously through a small incision in the skin or through a natural cavity or orifice (e.g., a nose or a mouth).
  • a medical imaging device e.g., a two-dimensional or three-dimensional ultrasound (“2DUS” or “3DUS") device, an X-ray fluoroscopy device, a magnetic resonance imaging (“MRI”) device and a computed tomography (“CT”) device.
  • 2DUS two-dimensional or three-dimensional ultrasound
  • MRI magnetic resonance imaging
  • CT computed tomography
  • non-imaging tracking technologies are used to localize the position of a medical device in order to reduce procedure time or to minimize exposure to ionizing radiation.
  • Current tracking systems may be based on sensing with electromagnetic, acoustic, impedance, and optical technologies, and may use principles such as signal strength (and/or attenuation), signal phase/frequency shifts, and/or time-of-flight to triangulate a sensor in 3-dimensional space.
  • Optical fiber based localization technology involves reconstructing a shape of an optical fiber by encoding geometric changes into the transmitted light.
  • shape reconstruction of an optical fiber may be performed by making use of variations in an optical refractive index that occur due to introduction of fiber Bragg gratings in the optical fiber or due to natural inhomogeneities in optical refraction arising from the manufacturing process of the optical fiber.
  • a fiber Bragg grating is a short segment of optical fiber that reflects particular wavelengths of light and transmits all others. This is achieved by adding a periodic variation of the refractive index in the fiber core, which generates a wavelength-specific dielectric mirror.
  • a fiber Bragg grating is sensitive to strain, which causes a shift in the Bragg wavelength ⁇ of the fiber Bragg grating in proportion to the magnitude of strain.
  • a primary advantage of using fiber Bragg gratings for distributed sensing is that a large number of deformation optic sensors may be interrogated along a length of a single optical fiber.
  • fiber deformation can be sensed using a Rayleigh scattering approach that exploits the natural variation in optical refractive index occurring along a length of an optical fiber.
  • the shape sensing ability of optical fiber is accomplished by measuring a three- dimensional ("3D") deformation at each sensed location along the length of the optical fiber starting from a proximal end of the optical fiber and ending at a distal end of the optical fiber.
  • 3D three- dimensional
  • Reconstruction is then possible by integration of strains along the fiber length or by using any of a multitude of estimation methods for solving inverse problems.
  • the process is integrative, meaning that the 3D location of one deformation optic sensor at one point along the optical fiber can only be computed if all the deformation optic sensors before that point in the optical fiber have also been reconstructed in 3D.
  • a surgeon may only be interested in a distal portion of the optical fiber that is near the anatomic region of interest.
  • the shape of the entire proximal portion of the optical fiber needs to be reconstructed including the part of the optical fiber outside of the patient's body.
  • the present invention provides a fiber segmentation technique for segmenting the optical fiber into an anchor fiber segment and an active fiber segment relative to an anchor point with the anchor fiber segment extending between a proximal endpoint of the optical fiber and the anchor point, and the active fiber segment extending between the anchor point and a distal endpoint of the optical fiber.
  • the fiber segmentation technique assumes the anchor point is fixed in space for fiber shape sampling purposes whereby, during a shape sampling of the optical fiber, the active fiber segment may be measured and reconstructed without having to measure and reconstruct the anchor fiber segment.
  • One form of the present invention is an optical shape sensing system employing one or more flexible optical fibers and a optical fiber controller for use in imaging an anatomical region of a body.
  • Each optical fiber includes an array of deformation optic sensors (e.g., a fiber Bragg gratings array) having a proximal endpoint and a distal endpoint.
  • a medical device e.g., a catheter, a needled, a tube or an endoscope
  • the optical fiber Upon being adjoined to a medical device (e.g., a catheter, a needled, a tube or an endoscope), the optical fiber is operated to generate an encoded optical signal indicative of each change in the shape of the optical fiber responsive to movement of the medical device within a defined space.
  • the optical fiber may be inserted within a lumen of a catheter whereby the shape of the optical fiber within and/or without the lumen changes as a distal tip of the catheter is navigated to an anatomical region of interest during a surgical procedure
  • the optical fiber controller processes the encoded optical signal for reconstructing a portion of or an entire shape of the optical fiber between the proximal endpoint and the distal endpoint.
  • the optical fiber controller segments the optical fiber into an anchor fiber segment and an active fiber segment relative to an anchor point having a sampling location within the defined space as designated by the optical fiber controller.
  • the anchor fiber segment extends between the proximal endpoint and the anchor point
  • the active fiber segment extends between the anchor point and the distal endpoint. More particularly, the anchor fiber segment is inclusive or exclusive of the proximal endpoint, and is inclusive or exclusive of the anchor point.
  • the active fiber segment is inclusive or exclusive of the anchor point, and is inclusive or exclusive of the distal endpoint.
  • the optical fiber controller sequentially reconstructs a shape of the anchor fiber segment of the optical fiber and a shape of the active fiber segment of the optical fiber.
  • the optical fiber controller exclusively reconstructs the shape of the active fiber segment of the optical fiber.
  • the optical fiber controller exclusively reconstructs the shape of the anchor fiber segment of the optical fiber.
  • FIG. 1 illustrates an exemplary embodiment of a medical imaging system in accordance with present invention.
  • FIGS. 2 and 3 illustrate exemplary embodiments of an optical fiber as known in the art.
  • FIG. 4 illustrates an exemplary embodiment of an optical fiber segmentation in accordance with the present invention.
  • FIG. 5 illustrates an exemplary embodiment of an optical fiber shape reconstruction in accordance with the present invention.
  • FIG. 6 illustrates an exemplary embodiment of the medical imaging system shown in
  • FIG. 1 in accordance with the present invention.
  • FIG. 7 illustrates an exemplary embodiment of a table of parameter input options in accordance with the present invention.
  • FIG. 8 illustrates an exemplary embodiment of a GUI parameter input option in accordance with the present invention.
  • FIG. 9 illustrates an exemplary embodiment of a fiber imaging parameter input option in accordance with the present invention.
  • a medical imaging system of the present invention employs an optical shape sensing system 10 and an imaging system 50 (e.g., an X-ray system, a MRI system, a CT system, an US system or a IVUS system).
  • an imaging system 50 e.g., an X-ray system, a MRI system, a CT system, an US system or a IVUS system.
  • optical fiber 30 that may be adjoined to a medical device 20 (e.g., a catheter, a needle, a tube or an endoscope).
  • a medical device 20 e.g., a catheter, a needle, a tube or an endoscope
  • optical fiber 30 is broadly defined herein as any article or device structurally configured for transmitting light by means of successive internal optical reflections via a deformation optic sensor array 31 having a proximal endpoint 3 lp and a distal endpoint 3 Id
  • each deformation optic sensor of array 31 is broadly defined herein as any article structurally configured for reflecting a particular wavelength of light while transmitting all other wavelengths of light whereby the reflection wavelength may be shifted as a function of an external stimulus applied to optical fiber 30.
  • optical fiber 30 and deformation optic sensor array 31 include, but are not limited to, a flexible optically transparent glass or plastic fiber incorporating an array of fiber Bragg gratings integrated along a length of the fiber as known in the art, and a flexible optically transparent glass or plastic fiber having naturally variations in its optic refractive index occurring along a length of the fiber as known in the art.
  • the term "adjoined” encompasses any manner by which optical fiber 30 is affixed to or contiguous with medical device 20.
  • optical fiber 30 being adjoined to medical device 20 include, but are not limited to, optical fiber 30 being inserted inside a lumen of a catheter or an endoscope as known in the art.
  • optical fiber 30 In operation with optical fiber 30 being adjoined to medical device 20, optical fiber 30 generates an encoded optical signal ("EOS") 32 via deformation optic sensor array 31 as known in the art that indicates a shape of optical fiber 30 at any instantaneous shape sampling of optical fiber 30 and more particularly over the course of multiple shape samplings, encoded optical signal 32 indicates each change to the shape of optical fiber 30 that occurs as medical device 20 is being moved within a defined space. Encoded optical signal 32 therefore facilitates a use of optical fiber 30 in visually displaying a position and orientation of medical device 20 within the defined space at any instantaneous time, and in visually displaying a movement tracking of medical device 20 within the defined space.
  • EOS encoded optical signal
  • encoded optical signal 32 will indicate the shape of optical fiber 30 at any instantaneous shape sampling of optical fiber 30 for visually displaying a position and an orientation of a catheter or an endoscope within a patient during a medical procedure, and more particularly over the course of multiple shape samplings, encoded optical signal 32 will indicate each change in the shape of optical fiber 30 due to movement of the catheter or the endoscope within the patient to thereby utilize optical fiber 30 for visually displaying a movement tracking of the catheter or the endoscope within the patient.
  • system 10 further employs an optical fiber controller 40 incorporating an optical interface 41 , a shape reconstructor 42 and a fiber segmenter 43 for processing encoded optical signal 32 to thereby periodically reconstruct a portion or an entire shape of optical fiber 30.
  • optical interface 41 is broadly defined herein as any device or system structurally configured for transmitting light through optical fiber 30 from proximal endpoint 31p to distal endpoint 3 Id to receive encoded optical signal 32 as generated by the successive internal reflections of the transmitted light via deformation optic sensor array 31.
  • optical interface 41 includes, but is not limited to, an arrangement of an optical coupler, a broadband reference reflector and a frequency domain reflectometer as known in the art for transmitting light through optical fiber 30 from proximal endpoint 3 lp to distal endpoint 3 Id and for receiving encoded optical signal 32 as generated by the successive internal reflections of the transmitted light via deformation optic sensor array 31.
  • shape reconstructor 42 is broadly defined as any article or device structurally configured for processing encoded optic signal 32 to partially or entirely reconstruct the shape of optical fiber 30 and for generating fiber shape data 44 in an appropriate form that enables imaging system 50 to visually display an instantaneous position and orientation of medical device 20 and more particularly, a movement tracking of medical device 20.
  • An example of shape reconstructor 42 includes, but is not limited to, a reconstruction engine installed as software and/or firmware on any type of computer for implementing a known shape reconstruction technique.
  • a known shape reconstruction technique for correlating encoded optic signal 32 into strain/bend measurements that are integrated into a shape of optical fiber 30.
  • reconstruction engine may or may not be integrated into imaging system 50.
  • fiber segmenter 43 is broadly defined herein as any article or device for implementing the fiber segmentation technique of the present invention. Specifically, fiber segmenter 43 segments optical fiber 30 into an anchor fiber segment and an active fiber segment relative to an anchor point with the anchor fiber segment extending between proximal endpoint 3 lp and the anchor point, and the active fiber segment extending between the anchor point and distal endpoint 3 Id.
  • the anchor fiber segment may be inclusive or exclusive of the proximal endpoint 30 and active fiber segment may be inclusive or exclusive of the distal endpoint 3 Id.
  • the anchor point may or may not coincide with an array location of a deformation optic sensor, and therefore the anchor fiber segment, the active fiber segment or neither segment may be inclusive of the anchor point.
  • the fiber segmentation technique assumes the anchor point has a permanent or temporary fixed sampling location within the defined space associated with medical device 20 whereby, during a shape sampling of optical fiber 30, shape reconstructor 42 may measure and reconstruct the active fiber segment without having to measure and reconstruct the anchor fiber segment. More particularly, for a low spatial temporal shape sampling of optical fiber 30, shape reconstructor 42 will sequentially measure and reconstruct the shapes of the anchor fiber segment and the active fiber segment, and for a high spatial temporal shape sampling of optical fiber 30, shape reconstructor 42 will exclusively measure and reconstruct the shape of the active fiber segment.
  • fiber segmenter 43 may designate the anchor point as having a permanently or temporarily fixed sampling location within the defined space associated with medical device 20 for purposes of spatial temporal shape samplings despite the fact that the anchor point may or may not be moving within the defined space or alternatively, fiber segmenter 43 may periodically update the sampling location of the anchor point within the defined space based on an anchor point update sampling of optical fiber 30 involving an exclusive reconstruction of the anchor fiber segment.
  • fiber segmenter 43 may establish the anchor point at the boundary between a main body of the catheter and the steerable tip of the catheter.
  • the anchor fiber segment is within the main body of the catheter and the active fiber segment is within the steerable tip of the catheter.
  • Fiber segmenter 43 will instruct shape reconstructor 42 when to execute a low spatial temporal shape sampling of optical fiber 30 involving a sequential reconstruction of the shapes of the anchor fiber segment and the active fiber segment to thereby monitor and track both the main body and the steerable tip of the catheter within a patient.
  • Fiber segmenter 43 will also instruct shape reconstructor 42 when to execute a high spatial temporal shape sampling of optical fiber 30 involving an exclusive reconstruction of the shape of the active fiber segment to thereby only monitor and track the steerable tip of the catheter. And if applicable, fiber segmenter 43 will instruct shape reconstructor 42 when to execute an anchor point update sampling of optical fiber 30 involving an exclusive reconstruction of the shape of the anchor fiber segment to thereby update the sampling location of the anchor point within the patient.
  • fiber segmenter 43 may segment optical fiber 30 into the anchor fiber segment, the active fiber segment and an untracked fiber segment relative to the anchor point and a tracking point.
  • the anchor fiber segment extends between the proximal endpoint 3 lp and the anchor point
  • the active fiber segment extends between the anchor point and the tracking point
  • the untracked fiber segment extends between the tracking point and distal endpoint 3 Id.
  • the untracked fiber segment is of no consequence to the movement tracking of medical device 20 within the defined space and therefore allows for both low and high spatial temporal shape sampling of optical fiber 30 without having to measure and reconstruct the untracked fiber segment.
  • the tracking point may or may not coincide with an array location of a deformation optic sensor, and therefore the active fiber segment may or may not be inclusive of the tracking point.
  • fiber segmenter 43 utilizes various parameters for specifying conditions necessary for implementing the fiber segmentation technique of the present invention.
  • fiber segmenter 43 may utilize parameter(s) specifying (1) an initial sampling location of the anchor point along optical fiber 30, (2) if applicable, a time interval for updating the sampling location of the anchor point along optical fiber 30, (3) an initial length of the active fiber segment from the anchor point along optical fiber 30, (4) a time interval for updating the length of the active fiber segment based of a reconstruction speed specified by imaging system 50, and/or (5) if applicable, an initial sampling location of the tracking point along optical fiber 30.
  • fiber segmenter 43 may automatically generate the parameters and/or interactively receive parameter inputs.
  • fiber segmenter 43 includes, but is not limited to, a module installed as software and/or firmware on any type of computer for implementing the fiber segmentation technique of the present invention. In practice, fiber segmenter 43 may or may not be integrated into shape reconstructor 42 and/or imaging system 50.
  • FIGS. 2-5 A description of an exemplary shape reconstruction in accordance with the fiber segmentation technique of the present invention as shown in FIGS. 2-5 will now be provided herein to facilitate a further understanding of the present invention.
  • FIG. 2 shows an optical fiber 34 inserted within a lumen of catheter 21 and having one or more fiber Bragg gratings arrays 35 extending from a proximal endpoint 35p to a distal endpoint 35d.
  • optical fiber 34 may include any number of arrays 35 or more than one optical fiber may be utilized as would be appreciated by those having ordinary skill in the art.
  • optical fiber 34 may include three (3) fiber Bragg grating arrays 35 arranged at 120° spacing as required for three-dimensional bend sensing.
  • FIG. 3 A optical fiber 34 may include three (3) fiber Bragg grating arrays 35 arranged at 120° spacing as required for three-dimensional bend sensing.
  • optical fiber 34b are utilized with each optical fiber 34b having a single fiber Bragg grating array 35 and with each fiber Bragg grating array 35 arranged at 120° spacing as required for three-dimensional bend sensing.
  • optical fiber 34 may include four (4) fiber Bragg grating arrays 35 with an on-axis array 35(4) encircled by arrays 35(l)-35(3) arranged at 120° spacing.
  • optical fiber 34 has a permanent helical twist (now shown) to enhance the three-dimensional bend sensing.
  • FIG. 4 shows a segmentation of optic fiber 34 in accordance with fiber segmentation technique of the present invention.
  • an anchor point 36 is specified as being the boundary between main body 21a and steerable tip 21b of catheter 21 (FIG. 2) whereby optic fiber 34 is segmented into anchor fiber segment 37 and active fiber segment 38.
  • Anchor fiber segment 27 extends between proximal endpoint 35p and anchor point 36
  • active fiber segment 38 extends between anchor point 36 and distal endpoint 35d.
  • anchor fiber segment 37 may be inclusive of proximal endpoint 35p or may be exclusive of proximal endpoint 35p with an endpoint 37a for example, and anchor fiber segment 37 may be inclusive of anchor point 36 or exclusive of anchor point 36 with an endpoint 37b for example.
  • active fiber segment 38 may be inclusive of anchor point 36 or may be exclusive of anchor point 36 with an endpoint 38a for example, and active fiber segment 38 may be inclusive of distal endpoint 35d or exclusive of distal endpoint 35d with an endpoint 38b for example.
  • FIG. 5 shows a state diagram of an exemplary shape reconstruction of optical fiber 34 in accordance with the fiber segmentation shown in FIG. 4.
  • anchor point 36 of optical fiber 34 is moving within the patient space as the entire catheter 21 is being navigated to an anatomical region of interest within the patient.
  • the sampling state of optical fiber 34 is a low spatiotemporal shape sampling 60 that involves a sequential reconstruction of the shapes of anchor fiber segment 37 and active fiber segment 38.
  • the sampling state of optical fiber 34 is a high spatiotemporal shape sampling 61 that involves an exclusive reconstruction of the shape of active fiber segment 38. This will enable fast reconstruction of active fiber segment 38 for purposes of exclusively tracking steerable tip 21b of catheter 21.
  • the sampling state of optical fiber 34 is an anchor point update sampling 62 that involves an exclusive reconstruction of the shape of the anchor fiber segment 37.
  • the sampling state of optical fiber 34 returns to high spatiotemporal shape sampling 61 that again involves an exclusive reconstruction of the shape of active fiber segment 38.
  • the sampling state of optical fiber 34 Upon a determination 66 that the medical procedure is complete and catheter 21 may be removed from the patient, the sampling state of optical fiber 34 returns to low spatiotemporal shape sampling 60 that again involves a sequential reconstruction of the shapes of anchor fiber segment 37 and active fiber segment 38 until such time catheter 21 is removed from the patient.
  • any optical fiber in accordance with the fiber segmentation technique of the present invention for numerous medical procedures utilizing any type of medical device 20 suitable for supporting optical fiber 30.
  • a portion of the optical fiber is in the heart and moves with user manipulation of the medical device as well as patient cardiac and respiratory motion, but a remaining portion of the optical fiber is in the inferior vena cava and is relatively stable.
  • the inferior vena cava portion of the optical fiber provides a good candidate for locating the anchor point during high spatiotemporal shape sampling of the optical fiber.
  • a stent balloon positioning and deployment in which the distal portion of the medical device is focused solely around the stent region.
  • a portion of the optical fiber remote from the stent region provides a good candidate for locating the anchor point during high spatiotemporal shape sampling of the optical fiber.
  • FIGS. 6-9 A description of a more detailed exemplary shape reconstruction in accordance with the fiber segmentation technique of the present invention as shown in FIGS. 6-9 will now be provided herein to facilitate a further understanding of the present invention.
  • FIG. 6 shows a clinical setting having a patient 70 prepared for a medical procedure involving catheter 21 supporting optical fiber 34 and an X-ray device 51 controlling a C-arm 53 and displaying images on a image monitor 52.
  • An optical fiber controller 45 generates and/or receives parameters 46-49 as shown for implementing the fiber segmentation of optical fiber 34 as shown in FIG. 4.
  • a parameter IANCHOR 46 specifies a sampling location of an anchor point
  • a parameter IACTIVE 47 specifies a length of active fiber segment 38 from anchor point 36 to distal endpoint 35d or to any point between anchor point 36 and distal endpoint 35d.
  • a parameter tANCHOR 48 specifies a time interval for which the sampling location of anchor point 36 is to be updated if applicable.
  • a parameter tACTivE 48 specifies a time interval for which the shape of the active fiber segment 38 is to be updated.
  • FIG. 7 illustrates a Table 80 representing four (4) embodiments for generating and/or receiving parameters 46-49.
  • an automatic mode 81 during a pre-operative phase of a medical procedure involves optical fiber controller 45 automatically defining parameter IA N CHOR 46, parameter IACTI V E 47 and parameter tANCHOR 48 by rules based one or more previously acquired libraries of training data from similar interventions and/or based on one or more preference profiles from physicians with similar approaches/perspectives. Additionally, optical fiber controller 45 automatically defines parameter tACTivE 48 based on the maximum reconstruction speed of 45.
  • any other combination of three parameters among parameters 45-48 may be defined with the undefined parameter being determined based on the three defined parameters.
  • optical fiber controller 45 executes an anchor point calibration sampling that involves an analysis of several reconstructions of the shape of the entire optical fiber 34. Specifically, from the shape reconstructions, optical fiber controller 45 works backwards from the distal tip of optical fiber 34 in order to search for a point of optical fiber 34 that experiences minimal, if any, motion and automatically defines that point as anchor point for parameter
  • Parameters 47-49 may be automatically defined based on real-time processing of additional intra-operative data streams (e.g., fluoroscopy with X-ray device 51), and additional parameters that must be defined for this mode 82 include a duration of the calibration acquisition and a motion threshold used to choose anchor point.
  • additional intra-operative data streams e.g., fluoroscopy with X-ray device 51
  • additional parameters that must be defined for this mode 82 include a duration of the calibration acquisition and a motion threshold used to choose anchor point.
  • GUI graphical user interface
  • a color coded GUI may be presented having parameter inputs 95-98.
  • a parameter input IA N CHOR 95 specifies a sampling location of an anchor point 93 (e.g., a blue colored dot) along a length of the optical fiber for establishing an anchor fiber segment 90 (e.g., a yellow colored segment) and an active fiber segment 91 (e.g., a green colored segment) relative to an anchor point 93.
  • anchor fiber segment 90 is inclusive of both the proximal endpoint of the deformation optic sensor array (not shown) and anchor point 93
  • active fiber segment 91 is exclusive of anchor point 93 and inclusive of a termination point 94 (e.g., a blue colored dot).
  • a parameter input CTIVE 96 specifies a length of an active fiber segment 91 via termination point 94, which may coincide with a distal endpoint of the deformation optic sensor array (not shown) or alternatively establish an untracked fiber segment 92 (e.g., red colored segment) that is exclusive of termination point 94 and inclusive of the distal endpoint of the deformation optic sensor array.
  • an untracked fiber segment 92 e.g., red colored segment
  • a parameter input tANCHOR 97 specifies a time interval for which the sampling location of anchor point 93 is to be updated.
  • a parameter input tAcnvE 98 specifies a time interval for which the shape of the active fiber segment 91 is to be updated.
  • GUI may further allow for user-specified alarms (e.g., audible and/or visual cues) to be defined for indicating any deviation of shape reconstruction from user specific characteristics (e.g., a shape inaccuracy alarm due to undersampling in space or time based on optical sensing in conjunction with real-time fluoroscopic data).
  • user-specified alarms e.g., audible and/or visual cues
  • an imaging of the fiber may be presented on imaging monitor 52 whereby a user can graphically select the parameters by visually comparing a location of optical fiber 34 with a medical image in which shape of optical fiber 34 is displayed.
  • an anchor point 103 e.g., a blue colored dot
  • an anchor fiber segment 100 e.g., a yellow colored segment
  • an active fiber segment 101 e.g., a green colored segment
  • a termination point 104 may be guided along the displayed optical fiber for extending length of active fiber segment 101 to the distal endpoint of the displayed optical fiber or for establishing an untracked fiber segment 102 (e.g., a red colored segment).
  • anchor fiber segment 100 is inclusive of both a proximal endpoint of the deformation optic sensor array (not shown) and anchor point 103.
  • active fiber segment 101 is exclusive of anchor point 103 and inclusive of termination point 104, which may coincide with a distal endpoint of the deformation optic sensor array (not shown) or alternatively establish untracked fiber segment 102 as shown that is exclusive of termination point 104 and inclusive of the distal endpoint of the deformation optic sensor array.
  • optical fiber controller 45 executes a movement tracking of catheter 21 via optical fiber 34 in accordance with the state diagram of FIG. 5 or another shape reconstruction in accordance with the fiber segmentation technique of the present invention.
  • FBGs fiber optics for shape sensing or localization generally, including, for example, with or without the presence of FBGs or other optics, sensing or localization from detection of variation in one or more sections in a fiber using back scattering, optical fiber force sensing, fiber location sensors or Rayleigh scattering.

Abstract

La présente invention concerne un système de détection optique (10) qui met en œuvre une fibre optique flexible (30) et un dispositif de commande de fibre optique (40). Ladite fibre optique (30) comprend un ensemble capteur optique de déformation (31) doté d'un point d'extrémité proximal (31p) et d'un point d'extrémité distal (31d), et peut être conjuguée à un dispositif médical (20) pour produire un signal optique codé (32) qui indique un changement de forme de la fibre optique (30), réagissant au déplacement du dispositif médical (20) dans un espace défini. Le dispositif de commande de fibre optique (40) utilise le signal optique codé (32) pour reconstruire une partie ou une totalité d'une forme de la fibre optique (30) entre le point d'extrémité proximal (31p) et le point d'extrémité distal (31d). À cette fin, le dispositif de commande de fibre optique (40) segmente la fibre optique (30) en un segment de fibre d'ancrage et un segment de fibre active par rapport à un point d'ancrage dont un emplacement d'échantillonnage est fixé dans l'espace défini, tel que désigné par le dispositif de commande de fibre optique (40).
EP11716306A 2010-05-13 2011-03-30 Reconstruction de forme rapide de fibres optiques Withdrawn EP2568865A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US33430910P 2010-05-13 2010-05-13
PCT/IB2011/051366 WO2011141830A1 (fr) 2010-05-13 2011-03-30 Reconstruction de forme rapide de fibres optiques

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EP2568865A1 true EP2568865A1 (fr) 2013-03-20

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Families Citing this family (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP5993877B2 (ja) 2011-02-17 2016-09-14 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． 電気活性マップを提供するシステム
CN104470419B (zh) 2012-07-09 2018-08-17 皇家飞利浦有限公司 用于自适应图像引导的介入的方法和系统
EP2903552B1 (fr) * 2012-10-01 2017-07-05 Koninklijke Philips N.V. Enregistrement de polyligne à trois dimensions à l'aide de contraintes de forme
EP2904601B1 (fr) 2012-10-01 2021-04-28 Koninklijke Philips N.V. Système d'entraînement et d'aide aux décisions cliniques utilisant un dispositif de détection de la forme
JP6086741B2 (ja) * 2013-01-29 2017-03-01 オリンパス株式会社 走査型観察装置とその作動方法
CN105612447A (zh) * 2013-09-30 2016-05-25 皇家飞利浦有限公司 用于将光学形状感测使能的设备中的光纤扭曲最小化的系统和方法
EP3055646B1 (fr) * 2013-10-02 2020-12-16 Koninklijke Philips N.V. Suivi de dispositif utilisant un codage longitudinal
JP2019508174A (ja) * 2016-03-15 2019-03-28 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． 光ファイバー実形状感知式栄養チューブ
US11547489B2 (en) 2016-11-28 2023-01-10 Koninklijke Philips N.V. Shape sensing of multiple over-the-wire devices
CN110225710B (zh) 2017-02-01 2022-12-30 直观外科手术操作公司 用于图像引导的程序的配准的系统和方法
WO2019171357A1 (fr) * 2018-03-09 2019-09-12 The University Of Hong Kong Conception de dispositif de suivi par irm, fabrication et méthodes d'utilisation pour système robotique guidé par irm
EP4013338A4 (fr) 2019-08-12 2023-08-30 Bard Access Systems, Inc. Systèmes et procédés de détection de forme pour dispositifs médicaux
WO2021108688A1 (fr) 2019-11-25 2021-06-03 Bard Access Systems, Inc. Systèmes de détection de forme comprenant des filtres et procédés associés
US11850338B2 (en) 2019-11-25 2023-12-26 Bard Access Systems, Inc. Optical tip-tracking systems and methods thereof
CN110974198B (zh) * 2020-01-03 2021-01-08 武汉理工大学 可穿戴式生命体征监测装置及方法
US11474310B2 (en) 2020-02-28 2022-10-18 Bard Access Systems, Inc. Optical connection systems and methods thereof
US11931179B2 (en) 2020-03-30 2024-03-19 Bard Access Systems, Inc. Optical and electrical diagnostic systems and methods thereof
EP4171423A1 (fr) 2020-06-26 2023-05-03 Bard Access Systems, Inc. Système de détection de mauvais positionnement
EP4171373A1 (fr) 2020-06-29 2023-05-03 Bard Access Systems, Inc. Référence de cadre tridimensionnel automatique pour fibre optique
US11624677B2 (en) 2020-07-10 2023-04-11 Bard Access Systems, Inc. Continuous fiber optic functionality monitoring and self-diagnostic reporting system
CN216675721U (zh) 2020-08-03 2022-06-07 巴德阿克塞斯系统股份有限公司 布拉格光栅光纤波动感测与监测系统
CN114344514A (zh) 2020-10-13 2022-04-15 巴德阿克塞斯系统股份有限公司 用于光纤连接器的消毒罩及其方法
CN113671622B (zh) * 2021-08-26 2022-10-28 桂林电子科技大学 一种用于介入消融手术的多功能光纤及其制备方法
CN116785556A (zh) * 2023-06-25 2023-09-22 复旦大学附属肿瘤医院 全自动智能感应导尿管

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004251779A (ja) * 2003-02-20 2004-09-09 Fuji Photo Optical Co Ltd 長尺可撓部材の三次元形状検出装置
US20060013523A1 (en) * 2004-07-16 2006-01-19 Luna Innovations Incorporated Fiber optic position and shape sensing device and method relating thereto
US9186046B2 (en) * 2007-08-14 2015-11-17 Koninklijke Philips Electronics N.V. Robotic instrument systems and methods utilizing optical fiber sensor
US7702189B2 (en) * 2007-06-04 2010-04-20 Honeywell International Inc. Fiber optic chemical sensor
CN100478660C (zh) * 2007-09-27 2009-04-15 天津大学 高灵敏度光纤温度传感器
JP5535950B2 (ja) * 2008-03-12 2014-07-02 ザ トラスティーズ オブ ザ ユニバーシティ オブ ペンシルバニア 生理学的な活動を記録し変調するためのフレキシブルかつ拡張可能なセンサアレイ
US20090290147A1 (en) * 2008-05-21 2009-11-26 Qorex Llc Dynamic polarization based fiber optic sensor
US7720322B2 (en) * 2008-06-30 2010-05-18 Intuitive Surgical, Inc. Fiber optic shape sensor

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO2011141830A1 *

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