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WO2011070476A1 - Planification de traitement d'ablation et dispositif associé - Google Patents

Planification de traitement d'ablation et dispositif associé Download PDF

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Publication number
WO2011070476A1
WO2011070476A1 PCT/IB2010/055491 IB2010055491W WO2011070476A1 WO 2011070476 A1 WO2011070476 A1 WO 2011070476A1 IB 2010055491 W IB2010055491 W IB 2010055491W WO 2011070476 A1 WO2011070476 A1 WO 2011070476A1
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Prior art keywords
ablation
volume
treatment planning
image
needle
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PCT/IB2010/055491
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English (en)
Inventor
Pieter M. Mielekamp
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Koninklijke Philips NV
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Koninklijke Philips Electronics NV
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Priority to BR112012013557A priority Critical patent/BR112012013557A2/pt
Priority to US13/514,075 priority patent/US9125689B2/en
Priority to EP10798624A priority patent/EP2509527A1/fr
Priority to JP2012542652A priority patent/JP6035148B2/ja
Priority to RU2012128523/14A priority patent/RU2581714C2/ru
Priority to CN201080055751.3A priority patent/CN102647956B/zh
Publication of WO2011070476A1 publication Critical patent/WO2011070476A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T19/00—Manipulating 3D models or images for computer graphics
    • 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
    • A61B34/10—Computer-aided planning, simulation or modelling of surgical operations
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T15/00—3D [Three Dimensional] image rendering
    • G06T15/10—Geometric effects
    • G06T15/40—Hidden part removal
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T15/00—3D [Three Dimensional] image rendering
    • G06T15/50—Lighting effects
    • G06T15/503—Blending, e.g. for anti-aliasing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A61B2018/0293—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques using an instrument interstitially inserted into the body, e.g. needle
    • 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
    • A61B34/10—Computer-aided planning, simulation or modelling of surgical operations
    • A61B2034/101—Computer-aided simulation of surgical operations
    • A61B2034/102—Modelling of surgical devices, implants or prosthesis
    • A61B2034/104—Modelling the effect of the tool, e.g. the effect of an implanted prosthesis or for predicting the effect of ablation or burring
    • 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
    • A61B34/10—Computer-aided planning, simulation or modelling of surgical operations
    • A61B2034/107—Visualisation of planned trajectories or target regions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B2090/364—Correlation of different images or relation of image positions in respect to the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37—Surgical systems with images on a monitor during operation
    • A61B2090/376—Surgical systems with images on a monitor during operation using X-rays, e.g. fluoroscopy
    • A61B2090/3762—Surgical systems with images on a monitor during operation using X-rays, e.g. fluoroscopy using computed tomography systems [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B90/361—Image-producing devices, e.g. surgical cameras
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2210/00—Indexing scheme for image generation or computer graphics
    • G06T2210/41—Medical
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2219/00—Indexing scheme for manipulating 3D models or images for computer graphics
    • G06T2219/008—Cut plane or projection plane definition
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2219/00—Indexing scheme for manipulating 3D models or images for computer graphics
    • G06T2219/028—Multiple view windows (top-side-front-sagittal-orthogonal)
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/0002—Inspection of images, e.g. flaw detection
    • G06T7/0012—Biomedical image inspection

Definitions

  • the present invention relates to an ablation treatment planning method and to an ablation treatment planning and needle guiding method. Furthermore, the present invention relates to devices for performing such methods, to a computer program adapted for controlling such methods when executed on a computer and a computer-readable medium having stored thereon such computer program.
  • tumourous tissue In order to treat cancer, it may be necessary to remove or destroy tumourous tissue in a body of a patient. Due to advances in imaging technology and the availability of highly controllable medical devices, ablation technology is becoming a viable treatment option for a variety of non-resectable tumours.
  • RFA radio frequency ablation
  • RFA devices typically come with diameters of 1.2 to 1.6 mm and may produce ablation zones with a diameter of 1.5 - 7 cm.
  • cryo ablation Another widely available ablation therapy method is cryo ablation, where instead of heating the tissue, freezing is used to cause necrosis of tissue. In this method, cell death is due to rapid freezing of intercellular water.
  • special needles may be placed percutaneous, i.e. through the skin, into the tumour. Argon gas is delivered through the needle thereby producing an iced ablation volume of predictable size and shape.
  • Cryoablation devices typically come with diameters of 1.2 - 8 mm and may produce ablation zones having a diameter of 4 - 5 cm.
  • Microwave ablation is an upcoming thermal ablation technology in which tissue may be heated using microwaves.
  • Microwave ablation probes typically come with diameters of 1.2 - 5.7 mm and produce ablation zones having a diameter of 1.7 - 6 cm.
  • the predicted ablation volume within which a specific ablation device is intended to ablate/kill tumourous tissue are usually determined and supplied by the device manufacturers.
  • isotherms are generally specified at three different temperatures as shown in Fig. 1.
  • various volume regions 3a, 3b, 3c may be defined within an overall ablation volume 1 generated by a cryoablation needle 5 such that the surface of each volume region 3a, 3b, 3c is defined at a location having a respective temperature such as for example -40°, -20° and 0°.
  • a volume inside an isotherm has a temperature below the temperature value of the isotherm.
  • the 0°-isotherm defines the overall ablation volume 1 within which tissue is iced during cryoablation.
  • each of the ablation regions 3a, 3b, 3c as well as the overall ablation volume 1 corresponding to the 0°C-ablation region 3c may have an ellipsoid or spheroid shape.
  • the spheroid enclosing the highest temperature volume region 3c may have main axis having dimensions of 32 mm x 56 mm whereas the inner volume region 3a enclosed by the -40°C-isotherm may have dimensions of 14.5 x 34 mm.
  • An ice front may extend about 6 mm in front of a needle tip.
  • a patient is usually positioned in a CT or MRI scanner and one or more ablation needles are inserted into the tumourous tissue under guidance of real-time CT fluoroscopy or ultrasound.
  • the procedure is most often performed by an interventional radiologist in a radiology department of a hospital.
  • ablation needle placement i.e. an insertion of the ablation needle into the patient's body towards a correct location within the tumourous tissue such that a location and an orientation of the ablation needle is chosen such that during an ablation process all of the tumourous tissue is destroyed.
  • a preferred method of creating a large and/or complex ablation volume is to use a plurality of ablation needles with multiple overlapping ablation volumes.
  • overlapping ablation volumes may be mostly created in the mind of an interventional radiologist without visual feedback.
  • ablation isotherms are usually asymmetric sized, i.e. may have an ellipsoid shape, depending on a needle insertion direction, an effected area may be detemiined by both an ablation needle target location and an ablation needle insertion direction/orientation.
  • precise control of an effected ablation volume may be difficult without precise and reliable assistance by a user such as a surgeon or a radiologist, especially at oblique insertion angles of the ablation needle.
  • an ablation treatment planning method as well as for an ablation treatment planning and guiding method allowing to reliably plan an ablation volume within a region of interest comprising for example tumourous tissue within a patient and, optionally, subsequently guiding an ablation needle in order to locate and orient the needle such that the ablation volume is ablated during an ablation procedure.
  • it may be desired to provide such ablation treatment planning method allowing ablation needle delivery at oblique angles and allowing viewing of the ablation volume coverage at arbitrary plane orientations.
  • an ablation treatment planning device and an ablation treatment planning and guiding device adapted to perform or control such methods
  • a computer program element adapted for controlling or performing such methods when executed on a computer and a computer-readable medium comprising such computer program element stored thereon.
  • a success of a percutaneous ablation such as a radio frequency ablation, a cryo- ablation or a microwave ablation, may mainly depend on an accuracy concerning a location and an orientation with which an ablation needle is inserted, enabling to destroy an entire tumour while avoiding damages on other organs and minimizing risks of local reoccurrence.
  • the needle image planning/guiding system proposed therein has been invented by the applicant of the present invention and is also referred to as XperGuide.
  • This system may allow bringing percutaneous needle interventions back to the angio lab.
  • Such navigational tool may create an overlay of live fluoroscopy imaging and 3D soft tissue imaging that may provide information on needle path and target.
  • XperGuide may be used in a wide range of clinical procedures from biopsies and drainages to ablations.
  • XperGuide imaging may provide for a live 3D feedback on advancement of a needle for extra guidance and control during interventional procedure.
  • a 2D cross sectional averaged slice with an arbitrary orientation and slice thickness may be interpolated from a three-dimensional volume data set that describes a volume image.
  • Such three-dimensional volume data set may be acquired for example in computed tomography (CT) by calculating a sequence of two- dimensional tomograms that lie in an x-y-plane at predetermined z-coordinates.
  • CT computed tomography
  • such three-dimensional volume data may also be reconstructed from a set of 2D images acquired by means of a 3D rotational scan with an X-ray C-arm system.
  • elliptical cross-sectional areas of the ellipsoid isotherms within a chosen imaging plane may have to be determined in order to support flexible oblique delivery angles of an ablation needle resulting in arbitrarily oriented ablation volumes and arbitrary MPR viewing plane orientation.
  • an ablation treatment planning method comprising the following steps preferably in the indicated order is proposed: (a) acquiring, e.g. with X-ray imaging using a C-arm X-ray image acquisition device, a 3D image data set of a region of interest; (b) introducing 3D model data of an ablation volume into the 3D image data set; and (c) drawing at least one 2D image comprising a cross sectional MPR slice of the region of interest and the ablation volume within an MPR plane while using the MPR plane as a clipping plane.
  • an ablation treatment planning and guiding method comprising the steps of (i) planning an ablation volume within a region of interest using at least one 2D image drawn in accordance with the method according to the above-mentioned first aspect of the invention wherein a location and an orientation of the ablation volume is predetermined by a planned location and orientation of an ablation needle; and (ii) guiding the ablation needle into the region of interest in accordance with the planned location and orientation.
  • an ablation treatment planning device and an ablation treatment planning and guiding device adapted for performing or controlling the methods according to the above first and second aspect of the invention, respectively, a computer program element adapted for controlling a method according to the above-mentioned first and second aspect of the invention, respectively, and a computer- readable medium having stored thereon a respective computer program element are proposed.
  • a gist of the present invention may be seen as based on the idea to use a more graphics based approach in order to visualize an ablation volume to be planned within a 3D image of a region of interest such that the ablation area may be visualized in any desired viewing plane orientation.
  • specific image processing procedures such as clipping imaging planes, tagging portions of the 3D model data of the ablation volume through the desired MPR plane into a stencil buffer, blending such tagged portions to a colour buffer, culling an outside or an inside of the ablation volume model, merging of ablation volumes, model transformation for scaling, positioning and/or
  • transforming the 3D model data of the ablation volume in a predetermined direction, etc. may be advantageously used in order to visualize the ablation volume within the region of interest such that a physician may easily plan a subsequent surgical intervention and then guide the ablation needle(s) according to such plan.
  • a physician having a 3-dimensional image of a region of interest may plan an ablation intervention by experimentally inserting simulated ablation volumes having a predictable shape and size into the visualized region of interest within a physiological 3D image at a selectable location and a selectable orientation.
  • the ablation volume should be visualized within the physiological 3D image in a way such that the physician may easily determine whether all tumourous tissue is enclosed within the planned ablation volume.
  • a basic idea therein may be that, if an MPR image plane is used as a clipping plane while drawing an ablation volume of e.g. spheroid or ellipsoid shape, the 2D cross- sectional ablation areas may show up as portions of the spheroid/ellipsoid that have been cut away and that may show an inside of the spheroid/ellipsoid.
  • an ablation volume e.g. spheroid or ellipsoid shape
  • Fig. 1 shows regions of an ablation volume created by a cryo ablation needle.
  • Fig. 2, 2a, 2b, 2c show presentations of a spheroid ablation volume within a
  • FIG. 3D image with an undipped ablation volume (Fig. 3) and with clipped cross-sectional ablation areas taken at various MPR planes (Fig. 2a,b,c).
  • Fig. 3a,b show a representation of a plurality of spheroid ablation volumes wherein overlapping ablation areas are visualized in a superimposed way.
  • Fig. 4a,b show a representation of a plurality of spheroid ablation volumes wherein overlapping ablation areas are visualized in a non- superimposed way.
  • Figs. 5a-e show a planned overall ablation volume composed from three
  • Fig. 6 shows an ablation treatment planning device comprising a
  • a volume rendered image is shown. Such image may be based on a 3D image data set acquired with an X-ray imaging device from a region of interest.
  • an ablation treatment planning system 100 may comprise such X-ray imaging device such as e.g. a C-arm system as shown in Fig. 6 which is adapted to acquire a plurality of X-ray projection images under various image acquisition angles such that, finally, a 3D image data set may be generated from the plurality of 2D projection images.
  • an X-ray source 101 attached to a first end of a C-arm 109 may emit X-rays which are transmitted through a region of interest 103 within a patient (not shown) lying on a displaceable table 105.
  • the X-rays are then detected with an X-ray detector 107 attached to a second end of the C-arm 109.
  • the C-arm may be moved and rotated to various positions and orientation and various 2D projection images may be acquired and transmitted to a controller 111 comprising a computer and a memory.
  • the various 2D projection images may be used to generate a 3D image data set.
  • Such 3D image data set may represent a volume rendered image of the region of interest such as the image including a spine, some ribs and a kidney of a patient as shown in Fig. 2.
  • 3D model data of an ablation volume 1 are introduced.
  • the introduction of the 3D model data of the ablation volume into the 3D image data of the region of interest may be performed in a specific way using a stencil buffer such that 3D image data representing pixels may be
  • Figs. 2a, 2b, 2c show clipped cross-sectional ablation areas of the ablation volume 1 positioned in the kidney of the patient in a frontal view (Fig. 2a), lateral view (Fig. 2b) and an axial view (Fig. 2c).
  • clipping may mean that a clipping plane is used to clip, i.e. "hide", a region of the represented three-dimensional space.
  • a clipping plane may be a plane that separates the represented space into two regions, one region is included from the viewing volume, the other is excluded from the viewing volume. For example, if a half sphere would have to be drawn, a clipping plane may be used that "slices" a sphere and only draws half of it.
  • Figs. 2, 2a, 2b, 2c may not be optimum for practical use for a physician. Only the inside of the spheroid ablation volume 1 may be relevant whereas the outside thereof may be distracting and may even be present if the intersecting MPR plane is behind the ablation volume. Furthermore, the shaded rendering may fully hide important clinical information comprised in the 3D image data set.
  • a 3 -steps drawing sequence that uses a stencil buffer as for instance provided by OpenGL ® or DirectX ® is proposed: 1. In a first step, by culling its outside, only the inside of the spheroid ablation volume will be drawn/tagged through the MPR clip-plane in the stencil buffer;
  • a "stencil buffer” may be similar to the color buffer with the exception that pixels in the stencil buffer do not represent colors but may have an application-specific meaning.
  • the stencil buffer may not be directly visible in the finally drawn image like the color buffer, but bits in the stencil planes may form an unsigned integer tag that effects and may be updated by drawing commands, through stencil function and stencil operations.
  • the stencil function may control whether a fragment is discarded or not by a stencil test, and the stencil operation may determine how the stencil planes are updated as a result of that test.
  • the stencil test may be operated on 2D pixels during a final step of rasterization when drawing the 2D image. The test may be controlled by means of the StencilFunc.
  • the stencil operation is a comparison between the value in the stencil buffer for a destination pixel and a stencil reference value (specified for this operation). If stencilling is enabled, an application can control, using glStencilOp, what happens under three different scenarios: (1.) The stencil test fails; (2.) The stencil test passes but the depth test fails; and (3.) Both, the stencil test and the depth test pass.
  • the term "culling” refers to an operation used to reduce fill-limited drawings by backface or frontface removal. If a polygon normal is facing away from a viewer then it is "backfacing".
  • Backface culling is a process by which polygons (usually triangles) that are not facing a camera are removed from a rendering pipeline. For example, if one is drawing a sphere, half of its polygons are backfacing at any given time. Backface culling is enabled by default. Drawing backfaced polygons may be useful when two side shading is enabled to look from the inside or to draw the inside of partially open or clipped objects. If frontface culling is enabled, only the back/inside of an object is rendered.
  • modeling and viewing transformations are setup and the cross sectional volumes slices are interpolated and displayed.
  • the modeling and viewing transformation will be setup to configure the planned ablation orientation, position and scaling of the sphere.
  • the cross sectional elliptical projection is obtained by a three step process. glStencilOp(GL_KEEP, GL KEEP , GL REPLACE) ;
  • glStencilFunc (GL_ALWAYS, STENCILMASK ELIPSE INSIDE, , 0 ); glCo lorMask(GL_F ALSE , GL FALSE, GL FALSE, GL FALSE);
  • the inside of the projected sphere will be drawn, by culling the front-faces.
  • the stencil buffer is setup such that the pixels that will be drawn are labeled STENCILMASK ELIPSE INSIDE. Note that, as shown above, by drawing the inside, if the clipplane is in front of the center of the ablation, to much of the projected cross section is drawn. This will be corrected in the next step.
  • a correct model transformation that scales, positions and transforms the ablation area in a direction of an ablation needle is set up.
  • the ellipsoids are drawn as spheres in a scaled coordinate system.
  • the stencil buffer and clip plane will need to be initialized.
  • An example of a result of the above 3-step drawing sequence is shown in Fig. 3a. Therein, three overlapping ablation volumes la, lb, lc have been introduced into a 3D image. Overlapping ablation areas are drawn by the rendering scheme as described above.
  • FIG. 3b multiple isotherms represented as ablation regions 3a, 3b, 3c as they may be defined for the various cryoablation needles are visualized in three different colors (indicated in Fig. 3b as different patterns).
  • ablation area representations 2a, 2b, 2c having different transparency levels.
  • Such different transparency levels may complicate an image interpretation to be made by a physician.
  • a representation with a drawn 2D image in which a plurality of tagged portions corresponding to a plurality of ablation volumes are blended into the color buffer such that profiles representing the ablation volumes do not overlap may be a preferred visualization.
  • Such non-overlapping presentation may provide for an easier image interpretation, particularly in the case of multiple isotherms as shown in Fig. 4b.
  • glColorMask (GL_TRUE, GL TRUE, GL TRUE, GL TRUE); glCullFace( GL FRONT);
  • the ablation profile need to be drawn in a specific order.
  • the profiles need to be drawn from inside out, so first all colder profiles then all less cold etc. This can be described as: for all ablations:
  • An orientation of the ablation volume in relation to a needle target location is usually defined by the device manufactures.
  • this relation is defined by the so-called Ice Front (in front of the needle tip).
  • the ablation volume can be drawn relative to the needle target location by a procedure as shown below. void DrawAblationIsoTerm(Vector3D& needleTarget, Matrixl6D& neeldleRotation, IsoTherm therm) ⁇
  • Vector3D dir needleRotation* Vector3D(0,0,l);
  • Vector3D ablatonTarget needleTarget+ (dir* (therm length- therm front)); glPushMatrixO;
  • gluQuadricDrawStyle (m ablation ellipse, GLU FLAT);
  • glColorMask (GL_FALSE, GL FALSE, GL FALSE, GL FALSE); glEnable( GL CULL FACE );
  • glStencilOp (GL_KEEP, GL KEEP, GL INCR); glColorMask(GL_TRUE, GL TRUE, GL TRUE, GL TRUE);
  • Fig 5 a shows three ablations, planned parallel next to each other, in the entry point view, i.e. the plane that is orthogonal to the needle directions.
  • Fig 5b, 5c, 5d, 5e show multiple orthogonal views on the same ablations. Note that the current needle 1 is shown in these presentations.
  • a C-arm X-ray imaging system may first be arranged such as to acquire images in the entry point view.
  • the needle is projected as a single point in the correct direction and without parallax as long as the C-Arm X-ray source is correctly oriented on the extension of the planned needle trajectory
  • the needle may then be inserted to a certain degree so as to be guided in its orientation.
  • the C-arm system may be rotated about 90° such as to acquire images in a plane including a longitudinal direction of the needle. In such orientation, a further insertion of the needle may be monitored and it may be observed whether the needle has finally attained its planned location.
  • the needles For the insertion of multiple needles it is advantageous to position the needles parallel to a first or a selected needle. In this way the ablation profiles/needles can be positioned in parallel relative to each other.
  • the needle target (ice front) and entry point (cross section with skin) may be calculated.
  • the ablation can be planned prior to the intervention on pre-interventional multi-modality data (MR/CT/XperCT) image data, and transformed to the interventional situation by means of 3D/3D registration, with a (fast scan) interventional acquisition.
  • MR/CT/XperCT multi-modality data
  • an ablation treatment planning and, optionally, guiding method usable for e.g. tumour tissue ablation with a cryoablation needle which cools down an adjacent tumour tissue to thereby generate an ablation volume is proposed.
  • a 3D image data set of a region of interest may be acquired by e.g. X- ray imaging using e.g. a C-arm system.
  • 3D model data of the ablation volume are introduced into the 3D image data set for example by tagging image pixels using a stencil buffer and possibly by culling specific inside areas and/or outside areas of the ablation volume.
  • a 2D image to be visualized to a physician and comprising a projection of the region of interest and the ablation volume is drawn wherein an MPR (multi planar reformatting) plane in which the 2D image is drawn is used as a clipping plane.
  • an ablation volume having any arbitrary shape such as for example an ellipsoid shape may be visualized within a 3D image space by drawing 2D images in any desired MPR plane such that also oblique orientations of the ablation volume can be represented.
  • an ablation needle may be guided to a location and in an orientation as previously planned.

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  • Image Processing (AREA)

Abstract

L'invention porte sur une planification de traitement d'ablation et, facultativement, sur un procédé de guidage utilisable pour une ablation de tissu tumoral, par exemple, au moyen d'une aiguille de cryo-ablation refroidissant un tissu tumoral adjacent afin de générer ainsi un volume d'ablation. Afin de pouvoir planifier un traitement d'ablation, un ensemble de données d'image tridimensionnelle d'une région d'intérêt peut être acquise au moyen par exemple d'une imagerie par rayons X, à l'aide par exemple d'un système de bras C. Ensuite, les données du modèle tridimensionnel du volume d'ablation sont introduites dans l'ensemble de données d'image tridimensionnelle, par exemple par le marquage de pixels d'image à l'aide d'un tampon pochoir et éventuellement par l'élimination de zones internes et/ou de zones externes spécifiques du volume d'ablation. Enfin, une image bidimensionnelle devant être visualisée par un médecin et comportant une projection de la région d'intérêt et du volume d'ablation est dessinée, un plan de reformatage multi-planaire (MPR), dans lequel l'image en deux dimensions est dessinée, étant utilisé comme plan de coupe. À l'aide d'une telle approche graphique, un volume d'ablation ayant une forme arbitraire quelconque, telle que par exemple une forme ellipsoïdale, peut être visualisée dans un espace d'image tridimensionnelle, en dessinant les images bidimensionnelles dans n'importe quel plan MPR voulu, de telle sorte que des orientations obliques du volume d'ablation peuvent aussi être représentées. Dans un procédé de guidage ultérieur, une aiguille d'ablation peut être guidée jusqu'à un emplacement et selon une orientation telle que celle prévue auparavant.
PCT/IB2010/055491 2009-12-08 2010-11-30 Planification de traitement d'ablation et dispositif associé Ceased WO2011070476A1 (fr)

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BR112012013557A BR112012013557A2 (pt) 2009-12-08 2010-11-30 método de planejamento de tratamento por ablação, método de guia e planejamento de tratamento por ablação, dispositivo de planejamento de tratamento por ablação, dispositivo de guia e planejamento de tratamento por ablição, elemento de progrma de computador e mídia legível em computador
US13/514,075 US9125689B2 (en) 2009-12-08 2010-11-30 Clipping-plane-based ablation treatment planning
EP10798624A EP2509527A1 (fr) 2009-12-08 2010-11-30 Planification de traitement d'ablation et dispositif associé
JP2012542652A JP6035148B2 (ja) 2009-12-08 2010-11-30 アブレーション治療計画及びデバイス
RU2012128523/14A RU2581714C2 (ru) 2009-12-08 2010-11-30 Планирование абляционного лечения и устройство
CN201080055751.3A CN102647956B (zh) 2009-12-08 2010-11-30 消融处置规划及设备

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US20120237105A1 (en) 2012-09-20
US9125689B2 (en) 2015-09-08
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