WO2010058339A2 - Système pour imager un milieu trouble - Google Patents

Système pour imager un milieu trouble Download PDF

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Publication number
WO2010058339A2
WO2010058339A2 PCT/IB2009/055115 IB2009055115W WO2010058339A2 WO 2010058339 A2 WO2010058339 A2 WO 2010058339A2 IB 2009055115 W IB2009055115 W IB 2009055115W WO 2010058339 A2 WO2010058339 A2 WO 2010058339A2
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WO
WIPO (PCT)
Prior art keywords
turbid medium
fluid
pressure
holder
imaging
Prior art date
Application number
PCT/IB2009/055115
Other languages
English (en)
Other versions
WO2010058339A3 (fr
Inventor
Levinus P. Bakker
Martinus B. Van Der Mark
Jacobus A. J. M. Deckers
Marjolein Van Der Voort
Anais Leproux
Original Assignee
Koninklijke Philips Electronics N.V.
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 N.V. filed Critical Koninklijke Philips Electronics N.V.
Publication of WO2010058339A2 publication Critical patent/WO2010058339A2/fr
Publication of WO2010058339A3 publication Critical patent/WO2010058339A3/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
    • A61B5/411—Detecting or monitoring allergy or intolerance reactions to an allergenic agent or substance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0091—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for mammography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/43—Detecting, measuring or recording for evaluating the reproductive systems
    • A61B5/4306—Detecting, measuring or recording for evaluating the reproductive systems for evaluating the female reproductive systems, e.g. gynaecological evaluations
    • A61B5/4312—Breast evaluation or disorder diagnosis
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
    • 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
    • A61B2562/14—Coupling media or elements to improve sensor contact with skin or tissue
    • A61B2562/146—Coupling media or elements to improve sensor contact with skin or tissue for optical coupling

Definitions

  • the invention relates to an imaging system for imaging a turbid medium.
  • the known imaging system comprises a base support and an inflatable component for holding an object to be examined between the inflatable component and the base support.
  • the inflatable component forms a pressure system which can apply pressure the to the object, notably a woman's breast.
  • a source of radiation emits a beam of light to the object and an optical detection system is aligned with the source of radiation.
  • the optical detection system receives radiation that passes through the object or is backscattered from the object.
  • the known imaging system applies, during the initial part of the examination, a smooth compression to a woman's breast from an initial pressure of 5-10mmHg to approximately 10-60mmHg.
  • the temporal evaluation of the detected optical image during this procedure reveals differences (in contrast) in the tissue's compressibility.
  • US 6,480,281 Bl discloses an imaging system in form of an optical mammography system in which a turbid medium such as a breast is accommodated in a measurement volume having the shape of a cup.
  • a turbid medium such as a breast
  • the space remaining between the inner cup boundary and the turbid medium is filled with a matching medium (in particular a matching liquid) to ensure, below others, optical coupling.
  • a matching medium in particular a matching liquid
  • a resilient sealing ring is provided to ensure reliable filling of the remaining space with matching medium.
  • An object of the invention is to provide an imaging system with a pressure system which is simple to operate and/or does not require a large number of additional components. Further, voids in a measurement volume shall be prevented and improved positioning of a turbid medium to be examined shall be achieved. Still further, improved differential imaging shall be allowed.
  • an imaging system for imaging a turbid medium comprising - a holder to receive the turbid medium and a fluid to surround at least part of the turbid medium and a pressure system to control the hydrostatic pressure of the fluid.
  • the imaging system of the invention comprises an illumination source to illuminate the object to be examined that is at least partly composed of the turbid medium.
  • the imaging system comprises a detection system to detect radiation from the object and a reconstruction unit to reconstruct an image of the interior of the object from the radiation levels detected by the detection system.
  • the object for example a woman's breast, is placed in a holder.
  • the holder may be formed as a conically shaped cup. The space between the object and the inner wall of the holder is filled with the fluid.
  • the matching medium is preferably formed by fluid.
  • the term fluid is not restricted to liquids but also covers e.g. gases and mixtures of gases and liquids.
  • the matching medium has optical scattering and/or refractive properties that (closely) match those of the turbid medium to be examined. Hence, perturbations are suppressed at the edge of the turbid medium of the distribution of propagation paths of the diffusely scattered radiation through the turbid medium.
  • the matching medium has optical properties, such as an absorption coefficient, similar to those of the turbid medium. In this way, boundary effects stemming from coupling light from the light into and out of the turbid medium are reduced and optical short-circuits around the turbid medium are prevented.
  • An optical short-circuit arises if light that has travelled throught the measurement volume but outside the turbid medium has been attenuated less than light that has travelled through the turbid medium.
  • the former light may dwarf the latter light at a photodetector unit for detecting light emanating from the turbid medium.
  • the hydrostatic pressure of the fluid can be controlled.
  • the hydrostatic pressure of the fluid is also applied to the turbid medium of the object.
  • the imaging system of the invention is able to image the turbid medium at controlled pressure conditions.
  • the imaging system of the invention is able to image the turbid medium at different pressures applied to the turbid medium by the fluid. From a comparison of the images made at different pressures in the turbid medium, inhomogeneities are distinguished from a homogeneous surrounding. For example, inhomogeneities having different responses to applied pressure, i.e. inhomogeneities having different elastic properties are distinguished.
  • the hydrostatic pressure to the turbid medium in the form of tissue, such as a woman's breast
  • blood pressure and blood flow in the tissue can be influenced.
  • irregularly vascularised tumour tissue can be distinguished from inhomogeneities having normal vascularisation.
  • the fluid is a matching medium, it can perform both the function of optical impedance matching between the turbid medium and its surroundings as well as the controlled application of hydrostatic pressure to the turbid medium. This achieves that, apart from the pressure system, no additional components are required.
  • Application of pressure to the fluid is relatively simple and only requires adequate sealing of the turbid medium in the holder. Such sealing also avoids that the fluid spills, while optimum surrounding of the turbid medium by the fluid is obtained.
  • the radiation from the object that is detected by the detection system can be radiation that has been applied to the turbid medium by the illumination source, propagated, mainly by multiple scattering through the turbid medium from which it subsequently exits. Part of the radiation is absorbed by the turbid medium and does not reach the detection system.
  • a fluorescent contrast agent may be employed that is excited by the radiation from the illumination source.
  • the fluorescent radiation e.g. fluorescent infrared radiation, propagates mainly by scattering through the turbid medium from which it exits and is detected. Images may be reconstructed from the detection of radiation from the illumination source having passed through the turbid medium, as well as detection of fluorescence from e.g. a contrast agent that is excited by radiation from the illumination source.
  • a fluorescent contrast agent is employed which accumulates preferentially in cancerous tumour tissue, so that a small cancerous tumour can be detected in an early stage of the pathology.
  • the pressure system is capable of applying expansion or compression to the fluid.
  • the pressure applied to the turbid medium can be lower of higher than ambient pressure. That is, the pressure system is able to apply either hypobaric as well as hyperbaric conditions to the turbid medium.
  • the imaging system has the further ability to distinguish inhomogeneities that react differently to the expansion or compression.
  • the pressure system is adapted to apply negative pressure inside the holder.
  • the turbid medium can be placed deeper in the measurement volume and is fixed relative to the holder. Occurrence of voids between the holder and the turbid medium can be prevented.
  • the holder is provided with a sealing ring comprising flexible lips.
  • the pressure system is adapted to cycle the pressure inside the holder between different pressures.
  • cycling means that the pressure is changed in one direction (e.g. to lower pressures) and thereafter changed in the opposite direction (e.g. to higher pressures).
  • the direction of pressure change is repeatedly changed several times.
  • differential imaging can be performed with images obtained at different pressures overlapping to a satisfactory extent.
  • the hydrostatic pressure is applied by a pump provided in the access duct that gives access to the interior of the holder.
  • the access duct is used to fill the interior of the holder with the fluid.
  • a pump is employed to supply the fluid into the holder.
  • the access duct has a vertical section in which the height of the fluid column is adjustable. Then, due to gravity the hydrostatic pressure in the fluid and the turbid medium is adjusted.
  • the pressure system supplies hydrostatic output pressures in the range of 6.66 to 16 kPa (50-120mmHg) and also smaller hydrostatic output pressures of about 1.33 kPa (lOmmHg) can be achieved.
  • the problem is also solved by a method of imaging an interior of a turbid medium, wherein the turbid medium is accommodated in a measurement volume and at least partly surrounded by a fluid; and measurements for imaging an interior of the turbid medium are performed at a plurality of different hydrostatic pressures inside the measurement volume.
  • a sealing ring is provided between a boundary of the measurement volume and the turbid medium and a sealing substance is applied between the sealing ring and the turbid medium.
  • a method of diffuse optical imaging is provided.
  • visible, including near infrared radiation having a wavelength in the range between 400nm to 1400nm is coupled into the turbid medium.
  • the radiation propagates diffusely, i.e. scattering dominates over absorption.
  • the control of the hydrostatic pressure may be performed by a computer programme which comprises instructions to coordinate control of the pressure system and control of the illumination source.
  • the computer programme enables that illumination of the turbid medium is performed under well defined hydrostatic pressure conditions.
  • the computer programme of the invention can be provided on a data carrier such as a CD-rom disk or a USB memory stick, or the computer programme of the invention can be downloaded from a data network such as the world- wide web.
  • Fig. 1 shows a schematic diagram of the apparatus for imaging a turbid medium of the invention
  • Fig. 2 shows a schematic cross-sectional drawing of an embodiment of the holder surrounding the measurement volume and the pressure system.
  • Fig. 3 shows a schematic cross-sectional drawing of another embodiment of the holder and the pressure system.
  • Figs. 4a to 4c schematically show three different types of sealing rings for the upper edge of the holder.
  • Fig. 5 shows a schematical graph for explaining the relation between pressure in the measurement volume, position changes of the turbid medium, and blood content of the turbid medium.
  • Fig. 1 shows a schematic diagram of the apparatus for imaging a turbid medium of the invention.
  • the apparatus for imaging a turbid medium shown diagrammatically in Fig. 1 is an optical mammography system.
  • the optical mammography system comprises a carrier 11 on which the patient to be examined (notably a woman whose breast(s) 1 are to be examined) is placed in prone position (i.e. face down) having one breast suspended in the examination space surrounded by a holder 2 that has the form of a measurement cup (see Fig. 2; it should be noted that not all reference signs are shown in Fig. 2 and some can only be found in Fig. 1).
  • the space between the breast 1 and the holder surface is filled with a fluid 22 as a matching medium, the scattering properties of which for example closely match the scattering properties of the average breast so that transitions of optical properties between the breast tissue and space outside the breast are reduced.
  • Fig. 2 shows a schematic cross-sectional drawing of the cup holder 2 with a breast 1.
  • a large number of fibres 23(510 in total) is connected with one end to the holder 2.
  • Half of the fibres are connected to detector modules 3 with the other end, and half of the fibres are connected to a fibre-switch 12 with the other end.
  • the fibre-switch 12 can direct light from three different lasers 24 in either one of the 256 source fibres 23 (255 to the cup, one directly to a detector fibre). In this way, either one of the source fibres 23 can provide a conical light beam in the holder.
  • all the source fibres will emit a conical light beam subsequently.
  • the light from the selected source fibre is scattered by the fluid and the breast, and is detected by the 255 detector modules.
  • Photodiodes are used as photosensors 3 in the detector modules.
  • the front-end detector electronics includes these photodiodes and an amplifier.
  • the amplification factor of the amplifier can be switched between several values.
  • the machine first measures at the lowest amplification, and increases the amplification if necessary.
  • the detectors are controlled by a computer 14, which has the function of a system controller. This computer 14 also controls the lasers, the fibre-switch, and the pump system.
  • the computer, holder, fibres, detectors, fibre-switch, and the lasers are all mounted into a bed as shown in Fig. 1.
  • a measurement starts with a holder 2 filled completely with the fluid 22, this is the calibration measurement.
  • a turbid medium 1 such as a breast is immersed in the fluid, and the measurement procedure is carried out again.
  • Both the calibration and the breast measurement consist of 255 ⁇ 255 detector output intensity signals (OIS) for each of the three lasers 24.
  • These detector output intensity signals (OIS) can be converted into a three dimensional image using a process called image reconstruction.
  • the reconstruction of the image of the breast from the detector output intensity signals is carried out by a reconstructor 4 that is usually implemented in software in the computer 14.
  • the reconstruction process which is based on for example an algebraic reconstruction technique (ART) or finite element method (FEM), finds the most likely solution to the (ill-defined) inverse problem.
  • ART algebraic reconstruction technique
  • FEM finite element method
  • the holder 2 is provided with an access duct 31 through which the holder can be filled with the fluid.
  • the access duct 31 can also be employed to drain fluid from the holder 2.
  • a sealing ring 32 is provided between the edge of the holder and the turbid medium 1, viz. the woman's breast.
  • the pressure system is formed by a pump 30 in the access duct 31 and the sealing ring 32.
  • the pump applies pressure to the fluid in the access duct 31 and in the holder 2.
  • This hydrostatic pressure is conveyed to the turbid medium formed by the tissue of the woman's breast.
  • the sealing ring 32 is adapted such that it ensures that hydrostatic pressure is applied and no fluid spills between the edge of the holder and the turbid medium when pressure is applied by the pump.
  • the pump is configured to apply at option, overpressure to the fluid and also underpressure to the fluid.
  • the pump 30 is controlled by the system control function implemented in the computer 14.
  • the computer 14 controls the imaging system to generate images of the turbid medium (e.g. the woman's breast) at several hydrostatic overpressure and underpressure values.
  • Figs. 4 a to 4c each show the sealing rings partly in section. All the sealing rings described with reference to Figs. 4 a to 4 c are compressible and elastic, and the lips which will be described in detail below are flexible. For example, silicone rubber is well-suited as a material for the sealing rings.
  • Fig. 4a shows the structure of a sealing ring 32a which has been optimized for applying a hydrostatic overpressure in the measurement volume surrounding the object turbid medium 1.
  • the sealing ring 32a has an least substantially ring-shaped structure comprising a central opening 40 through which the turbid medium 1 (the breast) is extended in the measurement volume surrounded by the holder 2.
  • the sealing ring 32a On the side facing the body of the, i.e. the upper side in Fig. 4a, the sealing ring 32a has a rounded shape adapted to snugly rest on the skin of the patient.
  • the inner side of the sealing ring 32a is provided with a flexible inner lip 41 which is slightly curved towards the side of the measurement volume.
  • the rounded upper edge 42 is slightly curved towards the measurement volume. Due to the curvature, the sealing ring 32a is capable to resist overpressures in the measurement volume. This is due to the fact that the sealing ring 32a will be pressed against the breast upon occurrence of overpresssures caused by the curved shape.
  • the sealing ring 32b shown in Fig. 4b differs from the sealing ring 32a shown in Fig. 4a in that, instead of the flexible inner lip 41 and the rounded upper edge 42, a solid rim 43 is provided which as rounded upper edge and comprises a curved surface on the side facing the measurement volume. Due to the solid structure, this sealing ring 32b is more robust but does not resist large positive or negative pressures in the measurement volume.
  • the sealing ring 32c shown in Fig. 4c is optimized for negative pressure (underpressure) in the measurement volume but also comprises satisfactory properties with respect to overpressures.
  • This sealing ring 32c differs from the sealing ring 32b shown in Fig. 4b in the following features.
  • the opening 40 On the side facing the measurement volume, the opening 40 has a first portion 40a comprising a wide diameter which tapers away from the measurement volume in a curved shape. Adjacent to this first portion 40a in the direction facing away from the measurement volume, a second portion 40b having a smaller diameter is formed.
  • a first lip 44 is formed on the inner side of the opening 40 on the side facing the measurement volume.
  • a widening, rounded upper third portion 40c Adjacent to the second portion 40b in the direction facing away from the measurement volume, a widening, rounded upper third portion 40c is formed which forms a rounded upper edge.
  • the outer circumference of the sealing ring 32c is provided with a recess 45 extending circumferentially.
  • a flexible second lip 46 extending away from the center of the opening 40 is formed. Due to the recess 45, if an overpressure is applied in the measurement volume, the first lip 44 will be pressed against the skin of the patient and tighten the sealing.
  • the sealing ring 32c shown in Fig. 4c provides satisfactory resistance with respect to both underpressure and overpressure.
  • this sealing ring is preferred.
  • a sealing substance is provided between the sealing ring 32 (e.g. 32a, 32b, or 32c) and the turbid medium 1 to be examined.
  • a suitable lubricating and sealing substance can be e.g.
  • the sealing substance can be applied to the turbid medium 1 before accommodation in the measurement volume or can be applied to the sealing ring 32.
  • the sealing substance has the effect that breaking the sealing between the turbid medium 1 and the sealing ring 32 (or between the patient and the measurement volume) can be prevented for high pressure differences between the measurement volume and the ambient environment.
  • the described properties have been verified in tests with volunteers for an optical mammography system. Pressures in the range between + 3 kPa and - 7 kPa (between + 30 mbar and - 70 mbar) could be reached in tests.
  • the access duct 31 is connected to a fluid reservoir 33 that is moveable vertically (as indicated by the double vertical arrow) so that the height of the fluid column in the vertical section 34 of the access duct changes. Due to gravity the pressure of the fluid is changed as the position of the reservoir 33 changes.
  • the moveable reservoir 33 forms the pressure system.
  • the movement of the reservoir 33 to control the hydrostatic pressure is controlled by the control function implemented in the computer 14. Also manual operation of the reservoir is possible.
  • a fluid column can be advantageously used in another way, as will be described in the following.
  • a fluid column can be advantageously used to apply (positive or negative) pressure to the measurement volume and thus to the turbid medium 1 accommodated therein in a convenient, reliable, and save manner.
  • a valve can be provided in the duct 31 which allows draining fluid from the duct 31 and the holder 2.
  • the fluid may be water. If fluid is drained, the level of the fluid in the fluid column will drop and consequently the pressure inside the measurement volume will drop. For increasing the pressure in the measurement volume, the level of fluid in the fluid column can be risen by adding fluid to the fluid column. This can e.g. be achieved by pouring additional fluid into an open fluid column or by providing an appropriate technical structure.
  • the fluid column may be provided with a scale correlated to the hydrostatic pressure in the measurement volume such that the currently achieved pressure level can easily be controlled by an operator.
  • a negative pressure (underpressure) is applied to the measurement volume for examination of the turbid medium 1.
  • Provision of a negative pressure has certain advantages which will be described in the following.
  • An advantage of applying negative pressure is that, due to the low pressure, the turbid medium 1 is positioned deeper in the measurement volume for examination. As a consequence, the field of view for the measurement is enhanced. Further, the turbid medium 1 is better kept in place, i.e. small movements of the turbid medium 1 which can deteriorate the measurement result can be prevented. This is particularly relevant in mammography where small movements of the patient such as breathing or coughing can lead to image artifacts in obtained images.
  • a further advantage of application of negative pressure is prevention of voids (e.g. air bubbles) in the measurement volume.
  • voids e.g. air bubbles
  • Such voids are actively removed after the turbid medium 1 is accommodated in the measurement volume and the negative pressure tightens the sealing between the turbid medium 1 and the measurement volume such that no new air or gas pockets will form in the measurement volume.
  • the turbid medium 1 can be stabilized against the inner boundary of the holder 2. In this case, the amount of fluid between the inner boundary and the turbid medium 1 is reduced. This results in a reduction of noise and attenuation caused by the fluid and thus helps improving image quality. Further, an a priori known, reproducible shape will be imposed to the turbid medium 1 such as a breast at least in the upper region of the measurement volume.
  • one of the challenges for optical imaging such as optical mammography is to obtain sufficient contrast and reproducibilty of the measurements.
  • a so-called contrast agent e.g. a fluorescent contrast agent
  • a so-called contrast agent may be injected into the blood stream of a patient or into the turbid medium 1. Since such a procedure is rather expensive and might cause complications such as unknown allergies, evaluating images taken under different circumstances can be an alternative.
  • Such an alternative is known as differential imaging.
  • a possibility for differential imaging is exploiting the difference in blood content or blood flow in the turbid medium 1 due to a difference in the (external) pressure applied to the turbid medium 1.
  • a plurality of mesasurements is performed and the pressure in the measurement volume is cycled between different pressures for these measurements.
  • Fig. 5 schematically illustrates the relation over time between a pressure change in the measurement volume and corresponding changes in position of the turbid medium (breast) and in the blood content in the turbid medium.
  • the time is plotted and the vertical axis indicates the pressure difference of the measurement volume with respect to the ambient pressure (solid line with straight sections), a difference of the breast position with respect to that at ambient pressure (curved solid line), and a change in blood content (dashed line; in arbitrary units), respectively.
  • the position of the turbid medium 1 in the measurement volume will depend on the history of pressure change in the measurement volume. This is due to the fact that the position of the turbid medium 1 and the blood distribution inside the turbid medium 1 will have a different time lag in responding to a pressure change inside the measurement volume. As a consequence, if the pressure is cycled between different pressures over time, a certain position and shape of the turbid medium 1 will occur more than once in the cycle but nevertheless correspond to different pressures and blood content, as can be gathered from Fig. 5.
  • a suitable situation for a measurement would be, for example, that at approximately 4 minutes in the diagramm of Fig. 5 where both the position and the blood content are at an extreme and thus do only vary slowly. This is beneficial for the stability of a measurement.
  • differential imaging turbid medium images overlapping to a satisfactory extent can be realized. This can result in improved images and may allow dispensing with the use of a contrast agent.
  • the fluid surrounding the turbid medium is preferably a matching medium
  • Another fluid such as a gas, e.g. ambient air, can be used as a fluid.
  • the fluid medium is chosen such that a hydrostatic pressure can be applied to the turbid medium.
  • the imaging system may also be an ultrasound system.
  • the disclosure is well suited for 3-D ultrasound applications such as whole-breast 3-D ultrasound for examination of female breasts. In whole breast ultrasound mammography, a transducer system is used to image the entire breast.
  • the turbid medium 1 i.e. the breast
  • the fluid can be further selected to have properties matching the properties of the turbid medium under examination with respect to ultrasound.
  • the fluid is selected to comprise properties matching the properties of average breast tissue with respect to ultrasound.

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Abstract

L’invention divulgue un système d’imagerie pour imager un milieu trouble (1), comprenant un support (2) destiné à recevoir le milieu trouble. Un fluide (22) entoure au moins une partie du milieu trouble. Un système de pression (30) commande la pression hydrostatique du fluide. En particulier, le système d’imagerie selon l’invention image le milieu trouble à des pressions différentes qui sont appliquées au milieu trouble par le fluide. À partir d’une combinaison des données mesurées ou d’images reconstituées effectuée à des pressions différentes dans le milieu trouble, les défauts d’homogénéité sont distingués par rapport à un environnement homogène. Le fluide peut être choisi pour exécuter à la fois la fonction de coïncidence d’impédance optique entre le milieu trouble et son environnement, ainsi que l’application commandée d’une pression hydrostatique au milieu trouble.
PCT/IB2009/055115 2008-11-21 2009-11-17 Système pour imager un milieu trouble WO2010058339A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP08169683 2008-11-21
EP08169683.3 2008-11-21

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WO2010058339A2 true WO2010058339A2 (fr) 2010-05-27
WO2010058339A3 WO2010058339A3 (fr) 2010-07-22

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998042248A2 (fr) * 1997-03-21 1998-10-01 Dynamics Imaging, Inc. Visualisation dynamique et fonctionnelle d'objets biologiques a l'aide d'un porte-objet non rigide
WO2000056206A1 (fr) * 1999-03-23 2000-09-28 Koninklijke Philips Electronics N.V. Dispositif de localisation destine a localiser un objet dans un milieu trouble
US6526309B1 (en) * 1995-01-03 2003-02-25 Non-Invasive Technology, Inc. Transcranial in vivo examination of brain tissue

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6526309B1 (en) * 1995-01-03 2003-02-25 Non-Invasive Technology, Inc. Transcranial in vivo examination of brain tissue
WO1998042248A2 (fr) * 1997-03-21 1998-10-01 Dynamics Imaging, Inc. Visualisation dynamique et fonctionnelle d'objets biologiques a l'aide d'un porte-objet non rigide
WO2000056206A1 (fr) * 1999-03-23 2000-09-28 Koninklijke Philips Electronics N.V. Dispositif de localisation destine a localiser un objet dans un milieu trouble

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