WO1998013715A1 - Microscope generant une representation tridimensionnelle d'un objet - Google Patents
Microscope generant une representation tridimensionnelle d'un objet Download PDFInfo
- Publication number
- WO1998013715A1 WO1998013715A1 PCT/FR1997/001695 FR9701695W WO9813715A1 WO 1998013715 A1 WO1998013715 A1 WO 1998013715A1 FR 9701695 W FR9701695 W FR 9701695W WO 9813715 A1 WO9813715 A1 WO 9813715A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- wave
- image
- microscope according
- point
- microscope
- Prior art date
Links
- 238000004364 calculation method Methods 0.000 claims description 21
- 238000012935 Averaging Methods 0.000 claims description 3
- 206010034759 Petit mal epilepsy Diseases 0.000 claims description 2
- 230000004048 modification Effects 0.000 claims 3
- 238000012986 modification Methods 0.000 claims 3
- 150000001768 cations Chemical class 0.000 claims 1
- 230000009466 transformation Effects 0.000 claims 1
- 230000003287 optical effect Effects 0.000 abstract description 27
- 238000001093 holography Methods 0.000 abstract description 6
- 238000009826 distribution Methods 0.000 abstract description 2
- 238000000034 method Methods 0.000 description 9
- 230000007547 defect Effects 0.000 description 6
- 238000000386 microscopy Methods 0.000 description 5
- 238000005286 illumination Methods 0.000 description 4
- 230000002441 reversible effect Effects 0.000 description 4
- 238000006243 chemical reaction Methods 0.000 description 3
- 238000005520 cutting process Methods 0.000 description 3
- 239000011521 glass Substances 0.000 description 3
- 238000007654 immersion Methods 0.000 description 3
- 238000004458 analytical method Methods 0.000 description 2
- 230000001427 coherent effect Effects 0.000 description 2
- 230000003247 decreasing effect Effects 0.000 description 2
- 238000001914 filtration Methods 0.000 description 2
- 230000006870 function Effects 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 230000010363 phase shift Effects 0.000 description 2
- 238000013519 translation Methods 0.000 description 2
- 229910000838 Al alloy Inorganic materials 0.000 description 1
- 230000000712 assembly Effects 0.000 description 1
- 238000000429 assembly Methods 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000001493 electron microscopy Methods 0.000 description 1
- 239000010438 granite Substances 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 230000004807 localization Effects 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 229910052754 neon Inorganic materials 0.000 description 1
- 238000000399 optical microscopy Methods 0.000 description 1
- 230000005693 optoelectronics Effects 0.000 description 1
- 230000003071 parasitic effect Effects 0.000 description 1
- 239000002245 particle Substances 0.000 description 1
- 230000010287 polarization Effects 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 238000012552 review Methods 0.000 description 1
- 238000004513 sizing Methods 0.000 description 1
- 238000001228 spectrum Methods 0.000 description 1
- 230000002123 temporal effect Effects 0.000 description 1
- 238000012546 transfer Methods 0.000 description 1
Classifications
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
-
- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03H—HOLOGRAPHIC PROCESSES OR APPARATUS
- G03H1/00—Holographic processes or apparatus using light, infrared or ultraviolet waves for obtaining holograms or for obtaining an image from them; Details peculiar thereto
- G03H1/0005—Adaptation of holography to specific applications
-
- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03H—HOLOGRAPHIC PROCESSES OR APPARATUS
- G03H1/00—Holographic processes or apparatus using light, infrared or ultraviolet waves for obtaining holograms or for obtaining an image from them; Details peculiar thereto
- G03H1/04—Processes or apparatus for producing holograms
- G03H1/08—Synthesising holograms, i.e. holograms synthesized from objects or objects from holograms
- G03H1/0866—Digital holographic imaging, i.e. synthesizing holobjects from holograms
-
- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03H—HOLOGRAPHIC PROCESSES OR APPARATUS
- G03H1/00—Holographic processes or apparatus using light, infrared or ultraviolet waves for obtaining holograms or for obtaining an image from them; Details peculiar thereto
- G03H1/0005—Adaptation of holography to specific applications
- G03H2001/005—Adaptation of holography to specific applications in microscopy, e.g. digital holographic microscope [DHM]
-
- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03H—HOLOGRAPHIC PROCESSES OR APPARATUS
- G03H1/00—Holographic processes or apparatus using light, infrared or ultraviolet waves for obtaining holograms or for obtaining an image from them; Details peculiar thereto
- G03H1/04—Processes or apparatus for producing holograms
- G03H1/0443—Digital holography, i.e. recording holograms with digital recording means
- G03H2001/0454—Arrangement for recovering hologram complex amplitude
- G03H2001/0458—Temporal or spatial phase shifting, e.g. parallel phase shifting method
-
- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03H—HOLOGRAPHIC PROCESSES OR APPARATUS
- G03H2226/00—Electro-optic or electronic components relating to digital holography
- G03H2226/11—Electro-optic recording means, e.g. CCD, pyroelectric sensors
Definitions
- Microscope generating a three-dimensional representation of an object
- the object of the invention is a device for obtaining a three-dimensional representation of the object and a complete representation of the diffracted wave by the latter in various lighting conditions, all in digital form then allowing any mode representation and any type of analysis
- This device includes an optical part allowing the generation of interference figures between a reference light wave and a light wave diffracted by the object observed, sensors making it possible to digitize these interference figures, actuators allowing to act on the optical svstemc, and a computer receiving the digitized interference figures controlling the actuators.
- a solution to reconstruct the light wave in the observed object is to make it interfere with a reference wave, the following principle of holography After registering l_ ⁇ interference pattern, the computer can perform a calculation equivalent rebuild operation to the optical operation used in holography But digital recording of a hologram is usually impossible because the variations in brightness are made over distances of 1 order of the wavelength, much less than the pitch of existing optoelectronic sensors.
- the reference wave used is an approximately sphe ⁇ quc wave and centered, actually or virtually, in one point close to the observed part of the object This allows to obtain figures of interference in when the intensity variations are done over higher characteristic distances, allowing digital recording and reconstruction by calculation equivalent to optical reconstruction
- the direct calculation of the light wave in the object according to a method simulating holographic reconstruction leads to defects which are the general defects of holography, namely the presence of a parasitic image symmetrical to the real image by relative to the point of origin of the reference wave and gaps of the second order with respect to the exact value of wave 1 in an advantageous version of the invention, the complex value (magnitude and phase) of the broadcast wave by the object and arriving on the receiving surface is calculated This then makes it possible to calculate the light wave in the object by direct application of the principle of reverse return of light, without the approximations linked to the holography. According to an advantageous version of the invention, this value is calculated from several interference figures differing from each other by the phase difference between the reference wave and the wave illuminating the object.
- the light wave from the ob j ct alone is then obtained by a simple, linear formula, from the three intensity records
- the interference pattern produced can be directly recorded by sensors located near the object, or it is possible to interpose optical elements deforming the wave between the object and the receiving surface.
- An advantageous version of the invention is forming an enlarged intermediate image of the object using a microscope objective This method makes it possible to spatially filter the intermediate image by interposing a diaphragm whose opening determines the size of the observed part of the object By decreasing the image size observed, the pixel size of the sensors required is decreased.
- a system of lenses located behind the diaphragm and suitably sized then allows the interference pattern to be formed.
- the reference wave can be superimposed on the wave coming from the object using a semi-transparent mirror interposed on the path of the light coming from the object
- the optical system is such that when a plane wave coming from the object, the image formed on the sensor in the reference wave is punctual abscence This allows to obtain directly a frequency representation of the wave coming from the object, each point of the sensor corresponding to a single frequency, that is to say a single wave vector, of the light wave coming from the object
- the three-dimensional representation obtained is presented as a complex quantity depending on the three spatial coordinates, corresponding to the light vibration at any point of the ob j and The result strongly depends on the lighting mode It is possible to use a parallel beam , spatially coherent.
- the representation obtained is then very precise in a plane orthogonal to the direction of the light beam but has defects in the direction parallel to this beam.
- use is made of lighting or the spatial coherence has been broken, c that is to say where the object is illuminated at any point in all directions This lighting is produced using a condenser forming in the plane of the object the image of a diffusing element illuminates by the laser beam. But the representation obtained is then grainy due to the temporal coherence of the lighting wave.
- This phenomenon called "Speckle” poses a problem already known in holographic microscopy.
- improves the performance of the j ob and using the wave diffracted by the object under several different lighting In particular, one can use multiple representations obtained by slightly moving the diffusing element between each picture. We can then average over all the representations obtained the intensity of Tonde at each point. This provides a satisfactory spatial representation of the object
- FIG. 1 shows the preferred embodiment of the invention.
- FIG. 2 shows an example of sizing relating to this embodiment.
- FIG. 3 indicates a particular configuration used during the adjustment procedure for this embodiment.
- Figure 4 relates to a variant of this embodiment differing by the user sample illumination.
- 5 shows a mechanical support for holding the whole device to the vertical.
- a laser (100) emits a ray which passes through a filter (101) and is then separated into light beams Fe and of reference Fr by a semi-reflecting plate (102).
- the light beam then passes through a lens (103) then is reflected by a mirror (104) and will strike a diffusing element (105) itself fixed on a motorized positioner with two axes (106) which can move it in an orthogonal plane to the optical axis of the objective (1 10).
- This condenser is itself fixed to a manual positioner an axis (108) which can move it in the direction of its optical axis.
- the focal distance of the lens (103) must be chosen so that the area of (105) illuminated by the beam is large enough so that its image by the condenser covers at least the entire area to be observed.
- This objective is a plane objective (which gives a plane image of a plane), with large aperture (for example 1.25), with immersion , and giving an enlarged image of the object at a finite distance.
- This microscope objective is attached to a focusing device (111).
- a diaphragm (112) is interposed allowing spatial filtering of the image. Behind this plane, an achromat (113) is positioned, the object focal plane of which must be merged with the image focal plane of the objective (1 10) A second achromat (115), the image focal plane of which is in the plane of a CCD sensor (116) forms in the plane of this CCD the image of the image focal plane of the objective (1 10).
- the CCD (116) is integrated into a camera (117) outputting an analog video signal.
- the reference beam first passes through a filter (1 18) then is reflected by a mirror (1 19) mounted on the mobile end of a piezoelectric translator (120) It then passes through a lens (121) which focuses the beam at a point
- the divergent beam from this point is partially reflected by the semi-reflecting mirror (114), which superimposes it on the beam from the object cl makes it possible to record their interference on the CCD (1 16)
- the point focusing the beam coming from the lens (121) must have its virtual image after reflection on the semi-transparent mirror (1 14) to the center of the image of the diaphragm (112) by one achromat (113) the piezoelectric translator (J20 ) modulates the phase of the reference beam
- the plane of the object must be horizontal so that the optical oil necessary to use the objective and the immersion condenser does not flow optics of 1 set is therefore vertical
- the camera (117) is mounted on a three-axis positioner in translation
- the laser (100) is mounted on an angular positioner allowing its direction to be adjusted
- the piezoelectric translator (120) is mounted on a positioner making it possible to adjust the direction of a axis orthogonal to the mirror plane (119) and to move the assembly (119) (120) in translation along this axis
- the mirror (104) is molded on a positioner making it possible to adjust the direction of an axis orthogonal to the plane of the mirror Le adjustment of these positioners is in principle carried out once and for all and in a mass production version of the system they can be eliminated in favor of more careful manufacturing. However, in this version intended for small series.
- the set is fixed on a support plate (500). the side of the plate opposite to the point of view of Fig 5 This plate is fixed to two triangular plates (501) and (502) themselves fixed to a square base (503)
- the plates (500) (501) (502 ) (503) are made of rigid aluminum alloy AU4G, for example 20 mm thick.
- the fixing of the plates can be done by screws and tapped holes, and must be made at a sufficient number of points to ensure perfect rigidity of the assembly This allows the system to be kept vertical while ensuring sufficient rigidity
- the assembly is placed on an anti-vibration support constitutes, for example, a granite plate placed on truck air chambers which absorb vibrations
- the assembly various elements on the plate (500), and in particular mirrors and semi-transparent mirrors, must be carried out in such a way as to ensure maximum rigidity of the assembly All the usual precautions must be taken in order to limit vibrations
- the condenser is a bright field condenser with immersion opening 1.2 whose opening diaphragm has in the open position a diameter of 28 mm
- the area of the diffusing element which is illuminated by the laser beam has a diameter D6 of about 1 cm.
- the distance D5 between this diffusing element and the condenser is 100 mm
- the microscope objective is a plane objective lOO with aperture 1.25, at a finite distance, forming the image at 160 mm from the neck of the objective, focal length approx.
- La distance D4 between the lens neck and the diaphragm is 160 mm
- Distance D3 between the diaphragm (1 12) and the achromat (1 13) is 20 mm
- the achromat (1 13) has a focal length of 200 m and a diameter of 30 mm and its most curved face is oriented towards the scmi -transparent mirror (114)
- the achromat (115) has the same characteristics and its most curved face is also oriented towards the mirror (1 14)
- the distance D2 between the two achromats is 85 mm, allowing the insertion of a semi-transparent mirror (1 14) of sufficient dimensions
- the distance between the achromat (1 15) and the CCD (1 16) is 200 mm
- the lens (121) has a diameter of 4mn ⁇ and a focal length of 6 mm the distance D7 between this lens and the optical axis is about 70 mm the distance D8 between the achromat (1 12) and the center of the mirror semi- transparent (1 14).
- the laser is a hey u -Neon wave length 633 nui has random polarization power of about 0.5 mW, 0.47 mm diameter beam from the sensor CCD is a square pixel sensor. the pixel surface being approximately 8.5 x 8.5 micrometers
- the camera outputs a CCIR video signal and a pixel clock
- the piezoelectric positioner (122) is a piezoelectric battery in the shape of a cylinder whose body is fixed and l he end moves 15 micrometers for an applied voltage of 100 Volts
- the calculation system is for example a PC type computer.
- the video signal acquisition card operating in real time, samples the signal on 8 bits and acquires images of 512x512 pixels sampled according to the clock pixel, therefore corresponding exactly to the CCD pixels
- the piezoelectric positioner is controlled directly by a digital / analog conversion card outputting a signal for example between zero and I ' m ⁇ , with for example
- V m ⁇ X 10 volts
- An RC filter with a time constant of approximately 0.1 ms is interposed between the output of the conversion card and the terminals of the piezoelectric actuator
- the positioner (106) is powered by stepper motors also controlled from the computer
- the computer will move it along the two axes in steps of 0.2 mm for example
- supp ⁇ mant (103) (105) (106 ) (107) (108) by inserting a mirror (300) returning the beam towards the lens, and using as a filter (118) a completely opaque element
- the miron (300) is mounted on an angular positioner which must be adjusted so as to target the input of the objective (1 10) and to maximize the intensity of the image received on (1 16)
- the position of (116) is then set in the a direction of the optical axis so that the image received on the sensor (1 16) is a point,
- the image received on the sensor (116) can be displayed in real time on the screen of the computer
- the reference beam must then be restored and the beam from the object must be removed by placing a cover behind the lens (1 10)
- the direction of the laser (100) must be adjusted so that viscr the center of the mirror (120)
- the position of the assembly (1 19) (120) must then be adjusted so that the beam from (120) actually passes through the lens (121)
- These settings can be controlled simply using a piece of light-diffusing paper
- the position of the unit (1 1) (120) must be refined so as to obtain the most intense and homogeneous lighting possible on the sensor (116)
- the reference beam must then be supp ⁇ me again and the beam from the object must be restored, the object used then being a simple transparent blade
- the position of (104) must be ieglec so as to target the diffusing element ( 105), then refined so that the image received on the sensor (1 16) is correctly centered.
- the positioner (108) must be governed so that the image received on the sensor, which represents the frequencies from the object or also a clear granular wide disc as possible During a change of observed object, it may be necessary to change the setting (108) but of (104) is normally fixed once and for all
- the values of optical density of the filters (101) and (118) must be constantly modified to have the most easily observable beam when it is observed with the naked eye or to have an optimal illumination of (1 16) when 1 image received on (1 16) is observed on the screen
- the automatic gain adjustment on the camera can advantageously be used
- the optical density values of the filters (1 1) and (1 18) must be chosen so that the reference beam and the beam coming from the object have close intensities when arriving at the CCD sensor, and that the interference pattern produced is as intense as possible without, however, the maximum value of the pixel recommended by the camera and the video digitization card being exceeded
- the lighting is changed by moving the diffusing element (105) using the positioner (106) At each position of the positioner, a different light is chosen
- the computer calculates the value complex (that is to say the complex number representing the phase and the intensity) of the light wave at any point of the object
- the final image of the object is obtained by averaging the intensities thus obtained for a number sufficient to separate illumination intensity of the wave at a point is the edge of the corresponding complex value Module to obtain the complex value of the light wave at any point on the objel
- I computer first calculates the complex value of the light wave coming from the object at any point of the CCD sensor This value is obtained from the recording of three interference patterns received on the sensor, the phase of the reference wave being offset by 120 degrees between each of these figures
- I ⁇ P, ⁇ the intensity at a point P of the sensor of the interference figure produced by the wave coming from the object and the reference wave for a phase shift ⁇ radians of the reference wave
- I re f
- Each pixel P of the sensor corresponds to a pure frequency of the wave in the object If we note (/,./) the coordinates (distance in pixels) of a point of the sensor relative to the central point of the area of interest, the pure frequency to which the point of coordinates (', /) corresponds, expressed in a coordinate system whose third axis is orthogonal to the plane of the sensor is then worth, has a constant factor near
- the computer generates the table S [i j] of complex numbers, for i and J varying from 0 to 51 1 by assigning to the elements of the table the following values
- the computer generates the table H of complex numbers representing the frequency of dimensions 512x512x512. in initializing to zero and then browsing the set of indices i and j varying from 0 51 1 by performing the operation
- the virtual point of origin of the reference wave is in the center, i.e. at the point of coordinates (256,256,256)
- Table F 1 constitutes the representation bidnnensionnelle of the wave in the plane of the object passing through the point of origin of the virtual orthogonal wave el reference to the optical axis (cutting) a section in a plane orthogonal to the above can be generated by calculating d 'first the table S2 [ij] of dimensions 512 ⁇ 512 in 1 adding to 0 then by browsing all the indices (i, j) by performing
- S [i, j] has the complex value of S2 i, - K 2 - (i - 256) " - (j - 256) C initially present
- the microscope is focused so as to have the sharpest possible picture bidnnensionnelle
- the above cycle is the simplest, but it can be optimized to take account overlaps between sensor exposure time and image transfer time
- the light wave calculation can be done on the whole object or on a part of the object, pa r example a cut, as a function of time and available calculation capacity In the simplest case.
- the computer generates and displays a simple section of the object
- the movement of the positioner (106) is done as indicated above, in steps of 0.2 mm in both directions
- the order in which these movements are carried out is indifferent provided that the N mm lights used to calculate the three-dimensional representation of the object are obtained from all distinct positions of the actuator (106), so as not to have the same lighting several times
- the passage at each cycle by the values 0 and V m ⁇ of the voltage limits the hysteresis effect of the piezoelectric actuator by always having the same cycle
- the calculation methods indicated above are not limiting
- the computer can generate three-dimensional representations showing portions of object more or lefs ranges (sections, projections, together sections to a limited thickness) It may filter these represenialioiis limiting 'grainy image at the cost of less definition treatment effeclue esl needed (speed of the image taken and definition calculation time RECL or different) and ii computing capacity of the computer
- a variant of this embodiment is to use a beam of light unidirectional This eliminates the need to perform an intensity niovcnnagc on plusieuis images because each point of the object is then illuminates with the same intensity movennage
- the intensity n elanl not necessary, the three-dimensional representation also preserves usable phase information.
- the images obtained are precise in the three dimensions only for certain particular types of objects, for example sub-microscopic particles included in glass. very precise in the plane orthogonal to the direction of the beam and has defects in the direction of the beam This lighting mode little! however be used in cases where one is satisfied with a two-dimensional image.
- This lighting can be made as shown in Figure 4 similar to Figure 3 to this close that the reference beam is no longer blocked and that an additional lens (400) must be inserted between the mirror (300) and the sample (109) This lens must be positioned so that its focal point coincides with the sample and its focal distance must be such that the diffraction spot formed on crossing the sample has approximately the diameter of the area observed.
- Another variant of this embodiment comprises an 'use only one interference pattern to generate a three dimensional representation
- This variant is the digital equivalent of the optical holographic reconstruction
- the piezoelectric actuator (120) n' is not used
- l (P) the intensity of the interference pattern produced at a point P of the sensor by the wave coming from the object and the reference wave
- the focusing point of the beam from the lens (121) must have its virtual image after reflection on the semi-transparent mirror (1 14) on the side of the image of one aperture (1 12) by one achromat ( 1 1). and not cenlrc as before the operation cvclc the microscope is modified in the sense that one image per esl used instead of three cycle or so nx laughed more action on the phase control svstemc
- the image is affected by second order approximations with respect to the ratio of the diffracted wave by the object to 1 reference wave
- the filters (1 1) and (1 18) must therefore be chosen so that the reference wave has a substantially greater intensity at the wave coming from the object entering the CCD. and not near intensities as before This choice must be refined so as to have in the three-dimensional representation the best compromise between bnnt and second order distortions
- the operation and the calculation mode are the same as before
- the generated three-dimensional representation includes the observed part of the object bounded by the diaphragm, and symmetrically with respect to virtual point of focusing of the beam from the lens (121)
- the aperture must be small enough to be visible on the representation obtained and its symmetric the area of the object that can be observed thus is smaller than in the preferred embodiment of this three-dimensional representation is also affected by second order approximations with respect to the ratio of the wave diffracted by the object at the reference wave, and the wave diffracted by the object must be much lower than the reference wave to obtain a convincing result II follows that the result obtained is much noisier than in the preferred embodiment
- the system is less sensitive to vibrations and allows images to be obtained more quickly
- This microscope can be used instead of conventional transmission microscopes in the field of biology or micromeasurement.
- the recording of the three-dimensional image is faster than with other methods, which facilitates the observation of samples.
Abstract
Description
Claims
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP97943004A EP0928433A1 (fr) | 1996-09-27 | 1997-09-26 | Microscope generant une representation tridimensionnelle d'un objet |
US09/254,869 US6249349B1 (en) | 1996-09-27 | 1997-09-26 | Microscope generating a three-dimensional representation of an object |
Applications Claiming Priority (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
FR9611773A FR2754069A1 (fr) | 1996-09-27 | 1996-09-27 | Microscope enregistrant l'onde diffractee par l'objet observe et l'utilisant pour calculer une representation en trois dimensions de cet objet |
FR96/11773 | 1996-09-27 | ||
FR96/15255 | 1996-12-12 | ||
FR9615255A FR2754070A1 (fr) | 1996-09-27 | 1996-12-12 | Microscope enregistrant l'onde diffractee par l'objet observe et l'utilisant pour carculer une representation en trois dimensions de cet objet |
FR9707469A FR2757278A1 (fr) | 1996-12-12 | 1997-06-17 | Microscope enregistrant l'onde diffractee par l'objet observe et l'utilisant pour calculer une representation en trois dimensions de cet objet |
FR97/07469 | 1997-06-17 |
Publications (2)
Publication Number | Publication Date |
---|---|
WO1998013715A1 true WO1998013715A1 (fr) | 1998-04-02 |
WO1998013715B1 WO1998013715B1 (fr) | 1998-06-04 |
Family
ID=27253235
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/FR1997/001695 WO1998013715A1 (fr) | 1996-09-27 | 1997-09-26 | Microscope generant une representation tridimensionnelle d'un objet |
Country Status (3)
Country | Link |
---|---|
US (1) | US6249349B1 (fr) |
EP (1) | EP0928433A1 (fr) |
WO (1) | WO1998013715A1 (fr) |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999053355A1 (fr) * | 1998-04-15 | 1999-10-21 | Vincent Lauer | Microscope generant une representation tridimensionnelle d'un objet et images generees par ce microscope |
FR2788139A1 (fr) * | 1999-01-06 | 2000-07-07 | Vincent Lauer | Microscope generant une represantation tridimensionnelle d'un objet et images generees par ce microscope |
WO2003002972A3 (fr) * | 2001-06-29 | 2003-11-20 | Univ Bruxelles | Procede et dispositif destines a l'obtention par microscopie d'images en trois dimensions d'un echantillon |
WO2013018024A1 (fr) | 2011-07-29 | 2013-02-07 | Ecole Polytechnique Federale De Lausanne (Epfl) | Appareil et procédé pour la tomographie de phase quantitative au moyen de balayage linéaire avec détection cohérente et non cohérente |
Families Citing this family (106)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2001021810A (ja) * | 1999-07-07 | 2001-01-26 | Nikon Corp | 干渉顕微鏡 |
JP4241038B2 (ja) * | 2000-10-30 | 2009-03-18 | ザ ジェネラル ホスピタル コーポレーション | 組織分析のための光学的な方法及びシステム |
US9295391B1 (en) | 2000-11-10 | 2016-03-29 | The General Hospital Corporation | Spectrally encoded miniature endoscopic imaging probe |
EP2333523B1 (fr) * | 2001-04-30 | 2020-04-08 | The General Hospital Corporation | Procédé et appareil permettant d'améliorer la clarté et la sensibilité de l'image en tomographie à cohérence optique au moyen d'une interaction permettant de contrôler les propriétés focales et la synchronisation de cohérence |
US7865231B2 (en) | 2001-05-01 | 2011-01-04 | The General Hospital Corporation | Method and apparatus for determination of atherosclerotic plaque type by measurement of tissue optical properties |
EP3252538B1 (fr) * | 2001-12-04 | 2019-02-06 | Ecole Polytechnique Federale De Lausanne (Epfl) | Appareil et procédé d'imagerie holographique numérique |
WO2003060423A2 (fr) * | 2002-01-11 | 2003-07-24 | The General Hospital Corporation | Appareil pour imagerie par tomographie a coherence optique a foyer en ligne axiale permettant d'ameliorer la resolution et la profondeur de champ |
US7355716B2 (en) | 2002-01-24 | 2008-04-08 | The General Hospital Corporation | Apparatus and method for ranging and noise reduction of low coherence interferometry LCI and optical coherence tomography OCT signals by parallel detection of spectral bands |
KR100438212B1 (ko) * | 2002-08-09 | 2004-07-01 | 학교법인고려중앙학원 | 전자현미경을 사용해서 물체의 3차원 공간 데이터를추출하는 방법 및 그 장치 |
EP2319405B1 (fr) * | 2003-01-24 | 2013-09-18 | The General Hospital Corporation | Système et procédé pour identifier des tissus à l'aide d'interférométrie à faible cohérence |
US8054468B2 (en) | 2003-01-24 | 2011-11-08 | The General Hospital Corporation | Apparatus and method for ranging and noise reduction of low coherence interferometry LCI and optical coherence tomography OCT signals by parallel detection of spectral bands |
WO2004088361A2 (fr) | 2003-03-31 | 2004-10-14 | The General Hospital Corporation | Reduction de granularite dans la tomographie par coherence optique au moyen d'une composition angulaire par codage de longueur de trajet |
KR101386971B1 (ko) * | 2003-06-06 | 2014-04-18 | 더 제너럴 하스피탈 코포레이션 | 파장 동조 소스용 방법 및 장치 |
US7095930B2 (en) * | 2003-07-17 | 2006-08-22 | Draka Comteq B.V. | Groove cable |
US7733497B2 (en) | 2003-10-27 | 2010-06-08 | The General Hospital Corporation | Method and apparatus for performing optical imaging using frequency-domain interferometry |
EP1687587B1 (fr) * | 2003-11-28 | 2020-01-08 | The General Hospital Corporation | Procede et appareil d'imagerie codee de maniere spectrale tridimensionnelle |
US7636157B2 (en) * | 2004-04-30 | 2009-12-22 | Ahura Corporation | Method and apparatus for conducting Raman spectroscopy |
US7499159B2 (en) * | 2004-04-16 | 2009-03-03 | Ahura Corporation | Method and apparatus for conducting Raman spectroscopy using a remote optical probe |
US7548311B2 (en) * | 2005-04-29 | 2009-06-16 | Ahura Corporation | Method and apparatus for conducting Raman spectroscopy |
AU2004320269B2 (en) * | 2004-05-29 | 2011-07-21 | The General Hospital Corporation | Process, system and software arrangement for a chromatic dispersion compensation using reflective layers in optical coherence tomography (OCT) imaging |
WO2006014392A1 (fr) | 2004-07-02 | 2006-02-09 | The General Hospital Corporation | Sonde d'imagerie endoscopique comprenant des fibres double gaine |
US8081316B2 (en) | 2004-08-06 | 2011-12-20 | The General Hospital Corporation | Process, system and software arrangement for determining at least one location in a sample using an optical coherence tomography |
WO2006024014A2 (fr) | 2004-08-24 | 2006-03-02 | The General Hospital Corporation | Ensemble procede, systeme et logiciel pour la mesure de la contrainte mecanique et des proprietes elastiques d'un echantillon |
US8208995B2 (en) | 2004-08-24 | 2012-06-26 | The General Hospital Corporation | Method and apparatus for imaging of vessel segments |
US20060088069A1 (en) * | 2004-08-30 | 2006-04-27 | Daryoosh Vakhshoori | Uncooled, low profile, external cavity wavelength stabilized laser, and portable Raman analyzer utilizing the same |
WO2006065267A1 (fr) * | 2004-08-30 | 2006-06-22 | Ahura Corporation | Spectrometre de profil bas et analyseur de raman utilisant ce dernier |
WO2006036434A2 (fr) * | 2004-08-30 | 2006-04-06 | Ahura Corporation | L'utilisation de couplage sans espace entre un ensemble laser, un ensemble tete de sonde optique, un ensemble spectrometre et/ou d'autres elements optiques d'application optiques portables telles que des instruments raman |
WO2006025876A2 (fr) * | 2004-08-30 | 2006-03-09 | Ahura Corporation | Laser raman a longueur d'onde stabilisee et a cavite externe insensible a la temperature et/ou aux contraintes mecaniques externes et analyseur raman utilisant ledit laser |
US7365859B2 (en) * | 2004-09-10 | 2008-04-29 | The General Hospital Corporation | System and method for optical coherence imaging |
EP2329759B1 (fr) | 2004-09-29 | 2014-03-12 | The General Hospital Corporation | Système et procédé d'imagerie à cohérence optique |
JP5175101B2 (ja) * | 2004-10-29 | 2013-04-03 | ザ ジェネラル ホスピタル コーポレイション | 偏光感応性光コヒーレンストモグラフィを用いて偏光非解消の偏光パラメータを測定するジョーンズ行列に基づく解析を行うシステム及び方法 |
JP5623692B2 (ja) * | 2004-11-02 | 2014-11-12 | ザ ジェネラル ホスピタル コーポレイション | 試料の画像形成のための光ファイバ回転装置、光学システム及び方法 |
US7995210B2 (en) | 2004-11-24 | 2011-08-09 | The General Hospital Corporation | Devices and arrangements for performing coherence range imaging using a common path interferometer |
JP2008521516A (ja) | 2004-11-29 | 2008-06-26 | ザ ジェネラル ホスピタル コーポレイション | サンプル上の複数の地点を同時に照射し検出することによって光学画像生成を実行する構成、装置、内視鏡、カテーテル、及び方法 |
EP2325803A1 (fr) | 2005-04-28 | 2011-05-25 | The General Hospital Corporation | Evaluation des informations de tomographie par cohérence optique pour une structure anatomique |
EP1887926B1 (fr) * | 2005-05-31 | 2014-07-30 | The General Hospital Corporation | Systeme et procede qui utilisent des techniques d'interferometrie d'heterodyne a codage spectral pour l'imagerie |
ES2354287T3 (es) | 2005-08-09 | 2011-03-11 | The General Hospital Corporation | Aparato y método para realizar una desmodulación en cuadratura por polarización en tomografía de coherencia óptica. |
CN101365375B (zh) | 2005-09-29 | 2013-09-11 | 通用医疗公司 | 用于经由谱编码进行光学成像的方法和设备 |
US7889348B2 (en) | 2005-10-14 | 2011-02-15 | The General Hospital Corporation | Arrangements and methods for facilitating photoluminescence imaging |
US7773645B2 (en) * | 2005-11-08 | 2010-08-10 | Ahura Scientific Inc. | Uncooled external cavity laser operating over an extended temperature range |
EP1971848B1 (fr) | 2006-01-10 | 2019-12-04 | The General Hospital Corporation | Systèmes et procédés de génération de données basés sur une ou plusieurs technique(s) d'endoscopie spectralement codées |
US20070223006A1 (en) * | 2006-01-19 | 2007-09-27 | The General Hospital Corporation | Systems and methods for performing rapid fluorescence lifetime, excitation and emission spectral measurements |
US8145018B2 (en) | 2006-01-19 | 2012-03-27 | The General Hospital Corporation | Apparatus for obtaining information for a structure using spectrally-encoded endoscopy techniques and methods for producing one or more optical arrangements |
PL1973466T3 (pl) | 2006-01-19 | 2021-07-05 | The General Hospital Corporation | Balonowy cewnik do obrazowania |
WO2007084959A1 (fr) * | 2006-01-20 | 2007-07-26 | The General Hospital Corporation | Systemes et procedes utilises dans la microscopie a effet tunnel a miroirs |
JP5524487B2 (ja) | 2006-02-01 | 2014-06-18 | ザ ジェネラル ホスピタル コーポレイション | コンフォーマルレーザ治療手順を用いてサンプルの少なくとも一部分に電磁放射を放射する方法及びシステム。 |
WO2007149603A2 (fr) | 2006-02-01 | 2007-12-27 | The General Hospital Corporation | Appareil destiné à appliquer une pluralité de rayonnements électromagnétiques à un échantillon |
WO2007149601A2 (fr) * | 2006-02-01 | 2007-12-27 | The General Hospital Corporation | Appareil destiné à commander au moins l'une d'au moins deux sections d'au moins une fibre |
JP5519152B2 (ja) | 2006-02-08 | 2014-06-11 | ザ ジェネラル ホスピタル コーポレイション | 光学顕微鏡法を用いて解剖学的サンプルに関わる情報を取得するための装置 |
EP1987318B1 (fr) | 2006-02-24 | 2015-08-12 | The General Hospital Corporation | Procédés et systèmes destinés à réaliser une tomographie par cohérence optique dans le domaine de fourier avec résolution angulaire |
WO2007109540A2 (fr) * | 2006-03-17 | 2007-09-27 | The General Hospital Corporation | Appareil, procédé et support accessible par ordinateur pour l'identification de caractéristiques d'au moins une partie d'un vaisseau sanguin compris à l'intérieur d'un tissu au moyen d'une interférométrie faible cohérence à domaine spectral |
JP5135324B2 (ja) * | 2006-04-05 | 2013-02-06 | ザ ジェネラル ホスピタル コーポレイション | サンプルの偏光感応性光周波数領域画像形成のための方法、構成およびシステム |
EP2517616A3 (fr) | 2006-05-10 | 2013-03-06 | The General Hospital Corporation | Processus, agencements et systèmes pour fournir une imagerie de domaine de fréquence d'un échantillon |
WO2007133964A2 (fr) * | 2006-05-12 | 2007-11-22 | The General Hospital Corporation | Processus, agencements et systèmes pour produire une carte d'épaisseur de couche de fibres sur la base d'images de tomographie à cohérence optique |
US7701571B2 (en) * | 2006-08-22 | 2010-04-20 | Ahura Scientific Inc. | Raman spectrometry assembly |
CN101589301B (zh) | 2006-08-25 | 2012-11-07 | 通用医疗公司 | 利用体积测定过滤技术来增强光学相干断层成像的装置和方法 |
WO2008049118A2 (fr) | 2006-10-19 | 2008-04-24 | The General Hospital Corporation | Dispositif et procédé d'obtention et de fourniture d'informations d'image associées à au moins une portion d' échantillon et permettant de réaliser une telle portion |
US7911621B2 (en) | 2007-01-19 | 2011-03-22 | The General Hospital Corporation | Apparatus and method for controlling ranging depth in optical frequency domain imaging |
US20080206804A1 (en) * | 2007-01-19 | 2008-08-28 | The General Hospital Corporation | Arrangements and methods for multidimensional multiplexed luminescence imaging and diagnosis |
US7949019B2 (en) | 2007-01-19 | 2011-05-24 | The General Hospital | Wavelength tuning source based on a rotatable reflector |
EP2602651A3 (fr) | 2007-03-23 | 2014-08-27 | The General Hospital Corporation | Procédés, agencements et appareil pour utiliser un laser à balayage de longueur d'ondes utilisant un balayage angulaire et des procédures de dispersion |
US10534129B2 (en) | 2007-03-30 | 2020-01-14 | The General Hospital Corporation | System and method providing intracoronary laser speckle imaging for the detection of vulnerable plaque |
WO2008131082A1 (fr) | 2007-04-17 | 2008-10-30 | The General Hospital Corporation | Appareil et procédés de mesure des vibrations à l'aide de techniques d'endoscopie spectralement codées |
US8115919B2 (en) | 2007-05-04 | 2012-02-14 | The General Hospital Corporation | Methods, arrangements and systems for obtaining information associated with a sample using optical microscopy |
JP5917803B2 (ja) | 2007-07-31 | 2016-05-18 | ザ ジェネラル ホスピタル コーポレイション | 高速ドップラー光周波数領域撮像法のためのビーム走査パターンを放射するシステムおよび方法 |
EP2191254B1 (fr) | 2007-08-31 | 2017-07-19 | The General Hospital Corporation | Systeme et procede pour une microscopie par fluorescence a auto-interference, et support lisible par ordinateur associe à ceux-ci |
US20090131801A1 (en) * | 2007-10-12 | 2009-05-21 | The General Hospital Corporation | Systems and processes for optical imaging of luminal anatomic structures |
WO2009059034A1 (fr) | 2007-10-30 | 2009-05-07 | The General Hospital Corporation | Système et procédé permettant une détection de mode de gaine |
JP5339535B2 (ja) * | 2007-11-22 | 2013-11-13 | 国立大学法人京都工芸繊維大学 | デジタルホログラフィ装置及び位相板アレイ |
US11123047B2 (en) | 2008-01-28 | 2021-09-21 | The General Hospital Corporation | Hybrid systems and methods for multi-modal acquisition of intravascular imaging data and counteracting the effects of signal absorption in blood |
US9332942B2 (en) * | 2008-01-28 | 2016-05-10 | The General Hospital Corporation | Systems, processes and computer-accessible medium for providing hybrid flourescence and optical coherence tomography imaging |
EP2274572A4 (fr) | 2008-05-07 | 2013-08-28 | Gen Hospital Corp | Système, procédé et support informatique permettant le suivi du mouvement des vaisseaux lors d'un examen en microscopie tridimensionnelle des artères coronaires |
WO2009155536A2 (fr) | 2008-06-20 | 2009-12-23 | The General Hospital Corporation | Coupleur fondu de fibres optiques et procédé associé |
WO2010009136A2 (fr) | 2008-07-14 | 2010-01-21 | The General Hospital Corporation | Appareil et procédés d'endoscopie couleur |
JP5731394B2 (ja) | 2008-12-10 | 2015-06-10 | ザ ジェネラル ホスピタル コーポレイション | 光サブサンプリングを通じて、光コヒーレンストモグラヒィーのイメージング深度範囲を伸ばすためのシステム、装置及び方法 |
WO2010085775A2 (fr) | 2009-01-26 | 2010-07-29 | The General Hospital Corporation | Système, procédé et support accessible par ordinateur permettant de fournir une microscopie de super-résolution à large champ |
CN102308444B (zh) | 2009-02-04 | 2014-06-18 | 通用医疗公司 | 利用高速光学波长调谐源的设备和方法 |
US9351642B2 (en) | 2009-03-12 | 2016-05-31 | The General Hospital Corporation | Non-contact optical system, computer-accessible medium and method for measurement at least one mechanical property of tissue using coherent speckle technique(s) |
BR112012001042A2 (pt) | 2009-07-14 | 2016-11-22 | Gen Hospital Corp | equipamento e método de medição do fluxo de fluído dentro de estrutura anatômica. |
ES2831223T3 (es) | 2010-03-05 | 2021-06-07 | Massachusetts Gen Hospital | Aparato para proporcionar radiación electromagnética a una muestra |
US9069130B2 (en) | 2010-05-03 | 2015-06-30 | The General Hospital Corporation | Apparatus, method and system for generating optical radiation from biological gain media |
US9557154B2 (en) | 2010-05-25 | 2017-01-31 | The General Hospital Corporation | Systems, devices, methods, apparatus and computer-accessible media for providing optical imaging of structures and compositions |
US9795301B2 (en) | 2010-05-25 | 2017-10-24 | The General Hospital Corporation | Apparatus, systems, methods and computer-accessible medium for spectral analysis of optical coherence tomography images |
EP2575591A4 (fr) | 2010-06-03 | 2017-09-13 | The General Hospital Corporation | Appareil et procédé pour dispositifs de structures d'imagerie, dans ou sur un ou plusieurs organes luminaux |
US9510758B2 (en) | 2010-10-27 | 2016-12-06 | The General Hospital Corporation | Apparatus, systems and methods for measuring blood pressure within at least one vessel |
WO2012149175A1 (fr) | 2011-04-29 | 2012-11-01 | The General Hospital Corporation | Moyens pour déterminer des propriétés physiques et/ou optiques résolues en profondeur de milieux de diffusion |
WO2013013049A1 (fr) | 2011-07-19 | 2013-01-24 | The General Hospital Corporation | Systèmes, procédés, appareils et supports accessibles par ordinateur permettant de produire une compensation de dispersion en mode polarisation dans la tomographie à cohérence optique |
US10241028B2 (en) | 2011-08-25 | 2019-03-26 | The General Hospital Corporation | Methods, systems, arrangements and computer-accessible medium for providing micro-optical coherence tomography procedures |
EP2769491A4 (fr) | 2011-10-18 | 2015-07-22 | Gen Hospital Corp | Appareil et procédés de production et/ou d'utilisation de retard(s) optique(s) de recirculation |
WO2013148306A1 (fr) | 2012-03-30 | 2013-10-03 | The General Hospital Corporation | Système d'imagerie, procédé et fixation distale permettant une endoscopie à champ de vision multidirectionnel |
WO2013177154A1 (fr) | 2012-05-21 | 2013-11-28 | The General Hospital Corporation | Appareil, dispositif et procédé pour microscopie par capsule |
JP6227652B2 (ja) | 2012-08-22 | 2017-11-08 | ザ ジェネラル ホスピタル コーポレイション | ソフトリソグラフィを用いてミニチュア内視鏡を製作するためのシステム、方法、およびコンピュータ・アクセス可能媒体 |
WO2014120791A1 (fr) | 2013-01-29 | 2014-08-07 | The General Hospital Corporation | Appareil, systèmes et procédés pour donner des informations sur la valvule aortique |
US11179028B2 (en) | 2013-02-01 | 2021-11-23 | The General Hospital Corporation | Objective lens arrangement for confocal endomicroscopy |
JP6378311B2 (ja) | 2013-03-15 | 2018-08-22 | ザ ジェネラル ホスピタル コーポレイション | 物体を特徴付ける方法とシステム |
WO2014186353A1 (fr) | 2013-05-13 | 2014-11-20 | The General Hospital Corporation | Détection de la phase et de l'amplitude d'une fluorescence auto-interférente |
EP3021735A4 (fr) | 2013-07-19 | 2017-04-19 | The General Hospital Corporation | Détermination de mouvement oculaire au moyen d'une imagerie de la rétine avec rétroaction d'un mouvement de l'oeil par imagerie de la rétine et fournir des informations en retour pour l'acquisition de signaux venant de la rétine |
WO2015009932A1 (fr) | 2013-07-19 | 2015-01-22 | The General Hospital Corporation | Appareil d'imagerie et procédé utilisant une endoscopie à champ de vision multidirectionnel |
EP3025173B1 (fr) | 2013-07-26 | 2021-07-07 | The General Hospital Corporation | Appareil avec dispositif laser utilisant de la dispersion optique pour applications en tomographie en cohérence optique dans le domaine de fourier |
US9733460B2 (en) | 2014-01-08 | 2017-08-15 | The General Hospital Corporation | Method and apparatus for microscopic imaging |
WO2015116986A2 (fr) | 2014-01-31 | 2015-08-06 | The General Hospital Corporation | Système et procédé pour faciliter une imagerie volumétrique manuelle et/ou automatique avec un retour de tension ou d'effort en temps réel au moyen d'un dispositif d'imagerie amarré |
WO2015153982A1 (fr) | 2014-04-04 | 2015-10-08 | The General Hospital Corporation | Appareil et procédé de commande de la propagation et/ou de la transmission d'un rayonnement électromagnétique dans un ou des guides d'ondes flexibles |
WO2016015052A1 (fr) | 2014-07-25 | 2016-01-28 | The General Hospital Corporation | Appareil, dispositifs et procédés d'imagerie in vivo et de diagnostic |
JP6762063B2 (ja) * | 2015-01-13 | 2020-09-30 | 国立大学法人電気通信大学 | 光学測定装置及び光学測定方法 |
JP6786858B2 (ja) * | 2015-06-19 | 2020-11-18 | 株式会社リコー | エレクトロクロミック化合物及びエレクトロクロミック組成物 |
EP3502695A1 (fr) * | 2017-12-22 | 2019-06-26 | IMEC vzw | Procédé et dispositif pour examiner et évaluer le cardiomyocyte |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3867009A (en) * | 1972-05-20 | 1975-02-18 | Romuald Pawluczyk | Holographic microscope with suppression of coherent noise |
US4974920A (en) * | 1989-04-17 | 1990-12-04 | General Electric Company | Electronic holographic apparatus |
JPH06258999A (ja) * | 1993-03-04 | 1994-09-16 | Takashi Yabe | 三次元物体の画像データ生成装置 |
Family Cites Families (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4869593A (en) | 1988-04-22 | 1989-09-26 | Zygo Corporation | Interferometric surface profiler |
US5042949A (en) | 1989-03-17 | 1991-08-27 | Greenberg Jeffrey S | Optical profiler for films and substrates |
US5633714A (en) * | 1994-12-19 | 1997-05-27 | International Business Machines Corporation | Preprocessing of image amplitude and phase data for CD and OL measurement |
-
1997
- 1997-09-26 US US09/254,869 patent/US6249349B1/en not_active Expired - Fee Related
- 1997-09-26 EP EP97943004A patent/EP0928433A1/fr not_active Withdrawn
- 1997-09-26 WO PCT/FR1997/001695 patent/WO1998013715A1/fr not_active Application Discontinuation
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3867009A (en) * | 1972-05-20 | 1975-02-18 | Romuald Pawluczyk | Holographic microscope with suppression of coherent noise |
US4974920A (en) * | 1989-04-17 | 1990-12-04 | General Electric Company | Electronic holographic apparatus |
JPH06258999A (ja) * | 1993-03-04 | 1994-09-16 | Takashi Yabe | 三次元物体の画像データ生成装置 |
Non-Patent Citations (9)
Title |
---|
BELTRAME F ET AL: "Three Dimensional Imaging of Cells through Digital Holographic Microscopy", PROCEEDINGS OF ISMIII '84: IEEE COMPUTER SOCIETY INTERNATIONAL SYMPOSIUM ON MEDICAL IMAGES AND ICONS, 24 July 1984 (1984-07-24) - 27 July 1984 (1984-07-27), ARLINGTON, US, pages 232 - 235, XP002056887 * |
BIANCO B ET AL: "Computer Simulation of 3-D Imaging in Holography: A Preliminary Study for Automated Holographic Microscopy", PROCEEDINGS OF ISMIII '82: FIRST IEEE COMPUTER SOCIETY INTERNATIONAL SYMPOSIUM ON MEDICAL IMAGING AND IMAGE INTERPRETATION, 26 October 1982 (1982-10-26) - 28 October 1982 (1982-10-28), BERLIN, DE, pages 32 - 35, XP002056886 * |
FRANÇON M: "Progress in Microscopy, Chapter III: Interference Microscopy in Transmitted Light", 1961, PERGAMON PRESS, XP002055327 * |
HARIHARAN P: "quasi-heterodyne hologram interferometry", OPTICAL ENGINEERING, vol. 24, no. 4, July 1985 (1985-07-01), BELLINGHAM US, pages 632 - 638, XP002055325 * |
KARPOV V B: "Study of Biological Samples with a Laser Fourier Holographic Microscope", LASER PHYSICS, vol. 4, no. 3, May 1994 (1994-05-01) - June 1994 (1994-06-01), RUSSIA, pages 618 - 623, XP002056885 * |
PATENT ABSTRACTS OF JAPAN vol. 018, no. 657 (P - 1842) 13 December 1994 (1994-12-13) * |
PLUTA M: "Holographic Microscopy", ADVANCES IN OPTICAL AND ELECTRON MICROSCOPY, ISBN 0-12-029910-0, vol. 10, 1987, ACADEMIC PRESS, LONDON, GB, pages 98 - 213, XP002055326 * |
SCHNARS U: "DIRECT PHASE DETERMINATION IN HOLOGRAM INTERFEROMETRY WITH USE OF DIGITALLY RECORDERD HOLOGRAMS", JOURNAL OF THE OPTICAL SOCIETY OF AMERICA - A, vol. 11, no. 7, 1 July 1994 (1994-07-01), pages 2011 - 2015, XP000454775 * |
TING-CHUNG POON ET AL: "THREE-DIMENSIONAL MICROSCOPY BY OPTICAL SCANNING HOLOGRAPHY", OPTICAL ENGINEERING, vol. 34, no. 5, 1 May 1995 (1995-05-01), BELLINGHAM, US, pages 1338 - 1343, XP000504997 * |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999053355A1 (fr) * | 1998-04-15 | 1999-10-21 | Vincent Lauer | Microscope generant une representation tridimensionnelle d'un objet et images generees par ce microscope |
FR2788139A1 (fr) * | 1999-01-06 | 2000-07-07 | Vincent Lauer | Microscope generant une represantation tridimensionnelle d'un objet et images generees par ce microscope |
WO2003002972A3 (fr) * | 2001-06-29 | 2003-11-20 | Univ Bruxelles | Procede et dispositif destines a l'obtention par microscopie d'images en trois dimensions d'un echantillon |
US7009700B2 (en) | 2001-06-29 | 2006-03-07 | Universite Libre De Bruxelles | Method and device for obtaining a sample with three-dimensional microscopy |
US7463366B2 (en) | 2001-06-29 | 2008-12-09 | Universite Libre De Bruxelles | Digital holographic microscope |
WO2013018024A1 (fr) | 2011-07-29 | 2013-02-07 | Ecole Polytechnique Federale De Lausanne (Epfl) | Appareil et procédé pour la tomographie de phase quantitative au moyen de balayage linéaire avec détection cohérente et non cohérente |
Also Published As
Publication number | Publication date |
---|---|
US6249349B1 (en) | 2001-06-19 |
EP0928433A1 (fr) | 1999-07-14 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
WO1998013715A1 (fr) | Microscope generant une representation tridimensionnelle d'un objet | |
EP1953580B1 (fr) | Dispositif de balayage optique confocal | |
EP2420822B1 (fr) | Dispositif destiné à l'obtention par microscopie d'images en trois dimensions d'un échantillon | |
EP1071974B1 (fr) | Microscope generant une representation tridimensionnelle d'un objet et images generees par ce microscope | |
EP1332397B1 (fr) | Microscope pour objets diffractants | |
EP2915009B1 (fr) | Système d'imagerie holographique auto-référencé | |
EP1524491A1 (fr) | Appareil associant un interféromètre et un microscope | |
EP3201563A1 (fr) | Methode et dispositif de microscope diffractive | |
EP2201420A2 (fr) | Système d'illumination structurée d'un échantillon | |
EP0376837B1 (fr) | Procédé et dispositif holographique en lumière incohérente | |
EP3602201B1 (fr) | Dispositifs et methodes d'imagerie optique par holographie numerique hors axe | |
WO2021260321A1 (fr) | Procédé de mise au point pour système d'imagerie holographique | |
FR2510292A1 (fr) | Dispositif servant a explorer point par point un objet | |
FR2917844A1 (fr) | Dispositif interferometrique | |
FR3081552A1 (fr) | Dispositif et procede d'observation d'un echantillon fluorescent par imagerie defocalisee | |
FR2638858A1 (fr) | Dispositif opto-mecanique de projection d'images et d'observation en trois dimensions | |
FR2777664A1 (fr) | Microscope generant une representation tridimensionnelle d'un objet et images generees par ce microscope | |
EP2486391A1 (fr) | Procede et systeme d'analyse structurelle d'un objet par mesure de front d'onde | |
FR3125893A1 (fr) | Système d’éclairage, notamment à usage de microscopie | |
WO2023194263A1 (fr) | Procédés d'imagerie microscopique de fluorescence et dispositifs de correction de front d'onde pour la mise en œuvre de tels procédés | |
EP0021982A1 (fr) | Procédé et dispositif de traitement optique d'objets par intercorrélation avec des anneaux | |
EP1321760A1 (fr) | Procédé de mesure de la fluorescence issue de microéchantillons et dispositif associé | |
FR2777665A1 (fr) | Microscope generant une image tridimensionnelle d'un objet et images generees par ce microscope | |
Martinez-Leon et al. | Short-coherence digital holography for the investigation of 3D microscopic samples | |
FR2754069A1 (fr) | Microscope enregistrant l'onde diffractee par l'objet observe et l'utilisant pour calculer une representation en trois dimensions de cet objet |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): BR JP US |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): AT BE CH DE DK ES FI FR GB GR IE IT LU MC NL PT SE |
|
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
WWE | Wipo information: entry into national phase |
Ref document number: 1997943004 Country of ref document: EP |
|
NENP | Non-entry into the national phase |
Ref country code: JP Ref document number: 1998515353 Format of ref document f/p: F |
|
WWP | Wipo information: published in national office |
Ref document number: 1997943004 Country of ref document: EP |
|
WWE | Wipo information: entry into national phase |
Ref document number: 09254869 Country of ref document: US |
|
WWW | Wipo information: withdrawn in national office |
Ref document number: 1997943004 Country of ref document: EP |