• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
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    • 专利摘要:
    Optical tomography apparatus comprising: a polychromatic light source (SLM), a one-dimensional optical sensor (CIM), an interferometric microscope (MI), a one-dimensional confocal spatial filtering system (FS, an actuation system (PR, TR1, TR2, TR3) for performing a unidirectional scanning in depth of an object to be observed and a processor (PR) for reconstituting a two-dimensional image of a section of said object from a plurality of one-dimensional interference images acquired by said sensor image during said unidirectional scanning Optical tomography method using such a device.
    公开号:FR3015659A1
    申请号:FR1363234
    申请日:2013-12-20
    公开日:2015-06-26
    发明作者:Arnaud Dubois
    申请人:Centre National de la Recherche Scientifique CNRS；Institut dOptique Graduate School；
    IPC主号:
    专利说明:

    [0001] The invention relates to an apparatus and an optical tomography method, intended in particular for biological and medical applications, and in particular histological applications.
    [0002] Histological examination of tissue taken by biopsy is of great use in clinical practice, for example in the diagnosis of tumors. However, this technique is slow and complex to implement because it requires a biopsy, that is to say, the taking of a sample of the tissue to be studied, and its cutting into thin slices which are observed under a microscope and analyzed. by an anatomopathologist. The complete procedure also requires the attachment of the sample, its occlusion in a matrix and its color. This is problematic especially in the case of examinations performed during surgical operations, where speed is of paramount importance. In addition, the sampling step can be dangerous for the patient, if not impossible (case of the brain, for example). For this reason, non-intrusive imaging techniques - especially optical - have been developed to visualize the internal structure of biological tissues - or more generally semi-transparent objects. In order to be competitive with conventional histological examinations, these techniques must allow access in situ to a depth of a millimeter below the surface of the tissue and have a resolution of one micrometer. Speed, simplicity and cost are also important parameters to consider. None of the known imaging techniques of the prior art gives full satisfaction. Optical Coherence Tomography (OCT) is a technique based on "white" (broadband) light interferometry. In its time domain version, a white light beam is divided into two parts, one focused on the tissue to be studied and the other on a reference mirror. The reflected (backscattered) light from the tissue is combined with that reflected by the reference mirror and detected by a photodetector. Interference occurs only when the optical path difference is at most on the order of the coherence length of the radiation; by changing the optical length of the reference arm of the interferometer, different depths in the tissue are accessed. An image with 2 or even 3 dimensions can be built thanks to the interferometry (which allows the acquisition according to the axial dimension, that is to say the depth) and to the sweep (which allows the acquisition according to one or two dimensions side). In the frequency domain scanning OCT, the reference arm has a fixed optical length and the interferometric signal is spectrally analyzed. See in this respect AF Fercher's article "Optical coherence tomography - principles and applications", Reports on Progress in Physics 66 (2003) 239-303. In practice, OCT makes it difficult to obtain better lateral resolutions. about a few micrometers. A more recent technique, full-field OCT, uses a two-dimensional image sensor to detect interferometric signals.
    [0003] This technique, coupled with the use of a light source of low temporal and spatial coherence such as a halogen lamp, makes it possible to appreciably improve the spatial resolution - both lateral and in depth (axial) - with respect to OCT scanning. However, this technique is poorly suited to applications in which the object is likely to move (especially for in vivo applications), thus causing interferometric signal interference. In addition, it provides "opposite" cuts (parallel to the surface of the observed object), while vertical cuts are often more useful. In addition, its depth of penetration is less than in scanning OCT. This technique is described, for example, in EP1364181 and in the article by A. Dubois, K. Grieve, G. Moneron, R. Lecaque, L. Vabre, and AC Boccara "Ultrahigh-resolution full-field optical coherence tomography ", Applied Optics 43, p. 2874 (2004). Confocal microscopy uses spatial filtering to select light from a small area of the observed object; a two- or three-dimensional image can then be reconstituted by scanning. EP 1 586 931 discloses a slit confocal microscope device and method which simplifies the image reconstruction process by allowing simultaneous acquisition of a plurality of line-arranged pixels. Confocal microscopy, used without fluorescent markers, offers significantly less penetration depth than in full scan OCT and full field OCT. The article by Yu Chen et al. "High-resolution line-scanning 5 optical coherence microscopy", Optics Letters Vol. 32, No. 14, July 15, 2007, pp. 1971 - 1973 discloses an apparatus and method combining slit confocal microscopy and scanning OCT to provide "face" cuts of a sample with higher sensitivity than in full field OCT. The axial resolution reached is about 3 μm and the lateral resolution is about 2 μm, these results being obtained using as a light source a very expensive femtosecond pulse laser. Nonlinear microscopy techniques (two-photon microscopy, harmonic generation, etc.) have performances in terms of depth of penetration, spatial resolution and acquisition rate - comparable to those of full field OCT, but at the cost of higher cost and generally longer acquisition times. The cost and complexity of implementation are also among the main disadvantages of non-optical imaging techniques, such as X-ray microtomography (which also has a low acquisition rate) and magnetic resonance imaging (MRI). spatial resolution is poor compared to optical methods). The invention aims to overcome at least some of the aforementioned drawbacks of the prior art. More particularly, it aims to provide a technique for visualizing the internal structure of semitransparent objects such as biological tissue making it possible to obtain vertical sections (orthogonal to the surface of the object) at a high rate (several cuts per second), with a high spatial resolution (of the order of 1 μm, both axially and laterally) and a satisfactory depth of penetration (of the order of a millimeter). The invention also aims to provide a technique suitable for in vivo and in situ applications. An object of the invention for achieving this purpose is an optical tomography apparatus comprising: a polychromatic light source; a one-dimensional optical sensor; an interferometric microscope comprising: a first arm, referred to as reference, at the end of which is arranged a so-called reference mirror; a second arm, called object; a beam splitter coupling said first and second arms to said polychromatic light source and said sensor; and at least one objective, said reference mirror being arranged in correspondence of a focusing plane of said objective or of said objective placed in the reference arm; a one-dimensional confocal spatial filtering system, cooperating with said polychromatic light source for illuminating an object to be observed, arranged at the end of said object arm, along a line, called said observation line, situated in said focus plane of said objective or an objective placed in the object arm, said one-dimensional confocal spatial filtering system being also arranged to select the light backscattered by said object and coming from said line of observation, and to form a one-dimensional image of said line on said sensor; characterized in that it further comprises: an actuation system configured to move said observation line parallel to an optical axis of said objective or said objective placed in the object arm so as to perform a unidirectional scanning of said object, while maintaining a zero optical path difference between, on the one hand, a first path from said beam splitter to said reference mirror and back by traversing said reference arm and, on the other hand, a second path from said splitter beam at said observation line and back by traversing said object arm; and a processor programmed or configured to reconstruct a two-dimensional image of a section of said object to be observed, oriented parallel to said optical axis of said objective or said objective placed in the object arm, from a plurality of one-dimensional interferometric images acquired by said sensor in correspondence of different positions of said line of observation during said unidirectional scanning. The one-dimensional optical sensor may, in some cases, be constituted by a line of pixels of a two-dimensional image sensor. According to various embodiments of such an apparatus: said actuating system may be configured to cause a relative displacement, parallel to said optical axis of said objective, or of said objective placed in the object arm, of said object to be observed by report to said interferometric microscope, without modifying the optical lengths of said reference arm and said object arm. Said actuation system may be configured to move the objective in the focusing plane of which said observation line is located and to modify the optical length of said reference arm so as to maintain zero the difference in optical path between said first path and said second path. The apparatus may also comprise a dispersion compensation device arranged on at least one of said object arm and said reference arm, said actuation system being configured to also act on said dispersion compensating device during said unidirectional scanning. Said interferometric microscope may be a Linnik microscope, comprising a first objective arranged on said reference arm and a second objective arranged on said object arm, said reference and object arms being disjoint. Alternatively, it may be selected from a Michelson microscope and a Mirau microscope, comprising a single lens. Another object of the invention is an optical tomography method comprising the following steps: a) providing a polychromatic light source; b) using a beam splitter to direct a first fraction of light emitted by said source along a first path, said reference path, and a second fraction of light emitted by said source along a second path, said object path; c) using an objective cooperating with a one-dimensional confocal spatial filtering system to focus said second light fraction so as to illuminate a semitransparent object to be observed along a line, called an observation line, located in a focusing plane said objective, and to collect the light backscattered by said object thus illuminated; d) using said objective, or other objective, to focus said first light fraction on a reference mirror arranged on said reference path, and to collect light reflected from said mirror; e) using said beam splitter to combine the light backscattered by said object with the light reflected by said mirror and direct it to a one-dimensional optical sensor; f) using said one-dimensional confocal spatial filtering system to select the light from said observation line, and to form a one-dimensional image on said sensor; g) using an actuation system to move said observation line parallel to an optical axis of said objective so as to perform a unidirectional scanning of an object to be observed on said object path, while maintaining a zero optical path difference between said reference path and said object path; and h) using a processor to reconstruct a two-dimensional image of a section of said object to be observed, oriented parallel to said optical axis, from a plurality of one-dimensional interferometric images acquired by said sensor in correspondence of different positions of said line of observation during said unidirectional scanning. According to various embodiments of such a method: Said step g) can be implemented by causing a relative displacement, parallel to said optical axis, of said object to be observed with respect to said interferometric microscope without modifying the optical lengths of said reference arm and said object arm. Alternatively, said step g) can be implemented by moving the objective in a focal plane of which said line of observation is located and by modifying the optical length of said reference arm so as to maintain zero the difference in optical path between said first path and said second path. The method may also comprise a step i) of compensating for the changes in the dispersion induced by the displacement of the observation line inside said object to be observed during said unidirectional scanning.
    [0004] Other characteristics, details and advantages of the invention will emerge on reading the description given with reference to the appended drawings given by way of example and which represent, respectively: FIG. 1A, a block diagram of a device optical tomography apparatus according to one embodiment of the invention, based on a Linnik interferometric microscope; FIG. 1B, a detail of an optical tomography apparatus according to a variant of said embodiment of the invention; FIGS. 2A, 2B, other possible embodiments of the invention based on the Michelson and Mirau interferometric microscope configurations; FIGS. 3A and 3B, the principle of confocal slit filtering; FIGS. 4A and 4B, respectively, an image obtained by using an optical coherence tomography apparatus according to the prior art and an image of the same object obtained by using an optical tomography apparatus according to the invention; and FIGS. 5A to 5F, various embodiments of the invention based on Michelson and Mirau interferometric microscopes and using an immersion medium. Figure 1A illustrates an optical tomography apparatus according to one embodiment of the invention. This apparatus essentially consists of a "Linnik" interferometric microscope modified by the addition of spatial filtering means (FE, FS), a compensation system (DCD) and dispersion gaps between the two arms of the interferometer. , a one-dimensional optical sensor (CIM) and a processor programmed or configured in a timely manner (PR). This apparatus comprises a polychromatic light source SLP. The latter is schematically represented by an incandescent bulb, but it may be preferably a higher luminance source, such as a light emitting diode or a combination of light emitting diodes, a superluminescent diode or a combination of electroluminescent light emitting diodes. superluminescent diodes, a halogen filament lamp, an arc lamp, or even a laser source or laser-based (source by generation of "supercontinuum" for example). In all cases, its spectral width (at mid-height) will preferably be greater than or equal to 100 nm; the greater this spectral width, the better may be the axial resolution of the device; the center-band wavelength may be visible or in the near-infrared range; in biological and medical applications, the near infrared is generally preferred, between 700 nm and 1500 nm. The source may be polarized or unpolarized, spatially coherent or inconsistent. Spatially coherent sources (of the laser or superluminescent diode type) may be advantageous because of their higher luminance, but they may introduce coherence "noise": parasitic interference phenomena resulting in a reduction in the relative amplitude of the interferometric signal useful and a lack of uniformity of lighting. In addition, the use of spatially coherent sources substantially increases the overall cost of the apparatus. A slot FE and a lens LE form an optical illumination system cooperating with the source SLP and the interferometric microscope to illuminate an object OBJ to be observed along a line having a width of the order of one micrometer (more precisely, the width of the line is of the order of magnitude of the lateral resolution of the imaging system). If the polychromatic light source is coherent, the FE slot may be replaced by beam shaping optics, incorporating for example a cylindrical lens, to illuminate the object along a line. The illumination beam formed by the LE lens is directed towards a beam splitter - in this case a splitter cube - SF. The latter directs a first portion of the incident beam along a first arm of the interferometric microscope, called "reference arm", BREF and a second portion of the incident beam following a second arm BOBJ, called "object arm". A first LO1 microscope objective and a so-called "reference" mirror MR are arranged on the reference arm; the objective focuses the light on the mirror, then collects the light reflected by it and redirects it - in the opposite direction of the arm, or path, reference. A second L02 microscope objective, of focal length identical to that of said first objective L01, is arranged on the object arm; the objective focuses the light on the object OBJ to observe, then collects the light backscattered by the latter and redirects it - in the opposite direction according to the arm, or path, object. Typically the objectives have a numerical aperture between 0.1 and 1.0 (unlike the traditional scanning OCT, there is no depth-of-field constraint here that would limit the numerical aperture to be used). It is worth noting that these goals can be in the air or at immersion; on the other hand, in the case of full-field OCT, immersion objectives are used, which may be restrictive in certain applications.
    [0005] The SF beam splitter recombines the light beams from the two lenses, allowing them to interfere, and redirects them along an arm called "observation" BOBS. The contrast of the interference fringes is maximum when the two beams that interfere have the same intensity; therefore, it may be advantageous to use a low reflection reference mirror or to provide an attenuator on the reference path. A one-dimensional spatial filter FS is arranged on the observation arm. In the embodiment of FIG. 1A, it is a confocal filter comprising two lenses LF1, LF2. A slot FO is placed in the rear focal plane of the lens LF1. The lens LF2 forms an image of the slot FO on the one-dimensional optical sensor CIM. The slot FO is optically conjugated to the slot FE associated with the source SLP; in other words, the interferometric microscope forms an image of the slot FE in correspondence of the slot FO and vice versa. As will be explained below, with reference to FIGS. 3A and 3B, this is a "confocal" configuration; in fact, the source SLP, the slot FE, the lens LE, the separator SF, the lens L02, the spatial filter SF form a confocal slot microscope. The one-dimensional optical sensor CIM (linear camera), consisting of a single row of pixels, detects the light at the output of the filter.
    [0006] It is also possible to use a single row of pixels of a matrix image sensor. In a variant (illustrated in FIG. 1B), the spatial filtering can be performed without the filtering system FS, by positioning the one-dimensional optical sensor CIM - whose pixels must be sufficiently small in the focal plane of a single lens LF. The use of a slit, however, is usually preferable because its width is adjustable. In addition, if an FO slot is present on the detector side (or the detector itself serves as a slot as explained above, FIG. 1B), it is possible to omit the lighting slot FE (or the system shaping the beam replacing it), at the cost of a decrease in detection sensitivity. The apparatus also comprises an actuating system constituted by a plurality of translation stages - TR1, TR2, TR3 and TRO - and by a PR processor driving them. All these stages of translation need not be present at the same time; in particular, if TRO is present, TR1 and TR2 may be omitted, and conversely if TR1 and TR2 are present, TRO may be omitted.
    [0007] The reference mirror unit MR and lens LO1 is moved axially by means of a first translational stage TR1 of said actuating system; therefore, the objective LO2 must also be moved, by means of a respective translation stage TR2, also forming part of said actuating system. When we go down (that is to say we translate in the direction of the object) the objective LO2 of a distance "e", we move the mirror of 2 reference object MR and the objective LO1 of nim - 1 - "e, nim being the index of nirn" refraction of the immersion medium of the objectives - gel, liquid or air (nim = 1) - and nobjet being the index of refraction of the object. As a variant, it would be possible to vary the axial distance between the single object OBJ and the interferometric microscope, while leaving the different elements of the interferometric microscope stationary.To do this, it is possible to move the whole interferometric microscope (displacement system not shown) or the OBJ object by means of the translation stage TRO, the latter case can be envisaged in particular with immersion objectives, in all cases, this has the effect of modifying the depth at which the object OBJ is probed: a LDO observation line, located in the focal plane of the objective L02, performs a scanning of said object "in depth", that is to say in the direction of the optical axis of said objective. The actuation system must both move this observation line and ensure that the optical path difference between the reference path and the object path (to the observation line) remains zero or at most less than coherence length of the polychromatic light source and the depth of field of the lens. This scan modifies the thickness of the object traversed by the light propagating along the object arm BOBJ, and therefore the dispersion that it undergoes. A DCD device is provided to compensate for this change in dispersion. The device DCD comprises a constant dispersion element ED1 - for example a glass block, a material which has a dispersion close to that of the object OBJ - arranged in one of the arms of the interferometer and a variable dispersion element ED2 disposed in the other arm of the interferometer. The ED2 element consists of two prisms arranged face to face; by moving one of the prisms relative to the other, the thickness of glass crossed, and therefore the optical path in this arm is modified. It is also possible to use a glass slide inclined with respect to the optical path; the crossed glass thickness is modified by acting on the angle of inclination. Other systems can be envisaged; the general idea is to vary the optical thickness in one of the arms in order to equalize the dispersion in the 2 arms of the interferometer (or at least reduce the gap) regardless of the depth imaging. In other embodiments, the dispersion compensation device may be constituted more simply by an immersion medium (typically a drop of liquid whose refractive index is close to that of the object) of which the Thickness in the object arm is reduced as the lens approaches the object to be observed (see Figures 5A-5F). In the embodiment of FIG. 1, the device DCD is actuated by a third translational stage TR3, also forming part of said actuating system. This allows a dynamic compensation of the dispersion, synchronized with the other displacements. Alternatively, a variable thickness of transparent dispersive material, such as glass, placed in one of the arms of the interferometer can be used to modify both the optical path and the dispersion. This variable thickness can be achieved through a double prism, such as the DCD device of Figure 1, or a simple swivel blade. In this case, it may not be necessary to move the objective assembly LO1 and mirror MR.
    [0008] The CIM detector acquires line images corresponding to a plurality of different positions of the line imaged in the object. This stack of image-lines can be processed numerically to obtain an image of a vertical section of the object. A simple approach is to use the so-called phase shift interferometry method, consisting of digitally combining several out-of-phase line images. For example, one can combine four line-images having a phase shift of rc / 2 between two adjacent images. If we denote by E 1, E 2, E 3, E 4 these images, (E 1 - E 3) 2 + (E 2 F 42 corresponds to the amplitude of the interference signal - that is to say to the amplitude of the the reconstructed image - and (E1-E3) -,., corresponds to the phase of the interference signal, E2-E4). This phase can provide other information than structural and tomographic information about the object. Alternatively, the line-image stack may be processed by Fourier analysis to extract the envelope from the interference fringes (the amplitude of the interference signal) and eliminate the unmodulated portion of the signal (non-signal). interferometric). It should be emphasized here that, according to the invention, the optical path on the two arms of the interferometer varies monotonically to generate an interferometric signal and, at the same time, perform a unidirectional depth sweep, without oscillations, of the observed object (of course, a second unidirectional scan can then be performed in the opposite direction). On the other hand, both in the aforementioned Yu Chen et al. in full-field OCT, there is no scanning of the depth of the object to acquire the interferometric signal. The latter is acquired thanks to a variable and periodic phase shift achieved by displacement of the reference mirror over a total range less than 1 micrometer typically.
    [0009] A three-dimensional image of the object can be obtained by juxtaposing images in adjacent sections. This requires scanning in a direction perpendicular to both the acquisition line and the optical axis of the lens L02. This scanning can be obtained by moving the object (or, equivalently, the interferometric microscope, or the illumination line) by means of a lateral translation stage. The same processor PR can drive the actuators TRI, TR2, TR3 and, if necessary, TRO (which may not be, or not be, only stages of translation) and treat the stacks of line images acquired by the CIM sensor, these tasks being interdependent. The processor PR may be a dedicated device, comprising one or more microprocessors, or a computer equipped with appropriate interface cards. As a variant, two different processors can be used for controlling the actuation system and for reconstructing the images.
    [0010] The invention has been described with reference to a particular embodiment, based on a Linnik interferometric microscope. However, other types of interferometric microscopes exist and are suitable for carrying out the invention. There may be mentioned, for example, the Michelson (FIG. 2A) and Mirau (FIG. 2B) microscopes comprising a single LO objective with a reference mirror MR and a beam splitter integral with said objective. These fixtures are simpler and more compact than Linnik's, but the introduction of an adjustable dispersion compensator is more difficult. Examples of embodiments based on the Michelson and Mirau configurations using an IM immersion medium to compensate for dispersion differences in the two arms of the interferometer are shown in Figures 5A (Michelson configuration with air lens), 5B (Michelson configuration with immersion objective), 5C (Michelson configuration with observation port HO and air lens - note that the porthole can be replaced by a hole and / or immersion objective), 5D (Mirau configuration with air lens), 5E (Mirau configuration with immersion objective) and 5F (Mirau configuration with surface objective and porthole - an immersion objective could also be used).
    [0011] Figures 3A and 3B recall the principle of operation of a confocal microscope slot. In a plane perpendicular to the spatial filtering slot FO (plane zy in FIG. 3A), the slot FO passes the light coming from the region of the object where the slot FE is focused by the objective LO (beam represented in FIG. solid line) and strongly attenuates light from other regions of the object (for example, dashed lines). In a plane parallel to the slot (plane zx in FIG. 3A), such a filtering does not occur. The result is that an LDO "line of sight" is defined in the focus plane of the lens and oriented like the FE and FO slots. An apparatus according to the invention thus comprises two means making it possible to select the light coming from a determined region of the object: the confocal filtering and the "coherence gate" defined by the "white" light interferometry. These means are complementary: confocal filtering improves the performance of interferometric imaging by eliminating the "background" produced by the scattering of light and parasitic reflections. All the dynamics of the sensor is thus used to detect the useful interferometric signal. Indeed, biological tissues are highly diffusing; the number of ballistic photons (which have not been diffused) decreases exponentially with depth. However, interferometry - even at short coherence length - does not distinguish between a ballistic photon from the region imaged in the object and a photon from other regions of the object and having traveled an optical path of same length because of the diffusions undergone. This results in a parasitic interferometric signal that adds to the useful interferometric signal, creating artifacts in the images and limiting the accessible imaging depth. In the device of the invention, the confocal filtering allows only the ballistic photons to pass, eliminating this background; admittedly, confocal slot filtering is not perfect because it only works in one dimension, but the reduction of this "background noise" remains important. Compared to confocal filtering alone, the use of interferometric detection allows considerable amplification of the useful signal (in the case of "pure" confocal microscopy, it is the low signal-to-noise ratio which limits the depth of acquisition). In the apparatus of the invention there is thus synergy - and not simple juxtaposition - between the two principles involved: low coherence interferometry microscopy and slit confocal microscopy. The use of confocal hole filtering, instead of confocal slot filtering, would significantly slow the acquisition of images (additional scanning would be required) without providing a significant benefit in terms of resolution and / or depth. accessible imagery.
    [0012] The technique of the invention is much better suited than full-field OCT for in vivo applications. In these applications, the "object" is a living organism (for example a patient) that is likely to move during the acquisition of the interferometric signal, interfering with it. According to the invention, an interferometric signal is acquired per line, in a very short time, for example of the order of 10-4 seconds, which makes it possible to overcome the problems of movement of the object. On the other hand, in full field OCT, the interferometric signal is acquired by combining several two-dimensional images acquired by a matrix camera, which is much longer.
    [0013] Compared to the aforementioned Yu Chen et al. Technique, the invention has the advantage of directly providing vertical slice images of the object observed, often more useful than "opposite" images. A prototype of the invention has been made using halogen lamp illumination, 0.15 numerical aperture lenses in air and a Linnik configuration. This prototype was tested using as an observed object a viewing card of an infrared beam of a thickness of about 500 μm, comprising two plastic layers enclosing a granular plastic containing microstructures, a non-diffusing region and a layer of fluorophores. The same object was imaged using a commercial scanning OCT device (ThorLabs). FIG. 5A shows the image (vertical slice) obtained with the commercial apparatus, FIG. 5B that obtained with the prototype of the invention. It can be noted how much the resolution is better in the case of the invention.
    [0014] It is interesting to note that, with appropriate sizing, an apparatus according to the invention can have a substantially "isotropic" spatial resolution, of the order of 1 μm both axially and laterally.
    权利要求:
    Claims (10)
    [0001]
    REVENDICATIONS1. Optical tomography apparatus comprising: - a polychromatic light source (SLP); - a one-dimensional optical sensor (CIM); an interferometric microscope (MI) comprising: a first reference arm (BREF), at the end of which is arranged a so-called reference mirror (MR); a second arm (BOBJ), called object; a beam splitter (SF) coupling said first and second arms to said polychromatic light source and said sensor; and at least one lens (L01, L02, LO), said reference mirror being arranged in correspondence of a focusing plane of said lens (LO) or said lens placed in the reference arm (L01); a one-dimensional confocal spatial filtering system (FS), cooperating with said polychromatic light source for illuminating an object to be observed (OBJ), arranged at the end of said object arm (BOBJ), along a line, called an observation line; (LDO), located in said focus plane of said objective (LO) or said objective placed in the object arm (L02), said one-dimensional confocal spatial filtering system being also arranged to select the light backscattered by said object and from said observation line (LDO), and to form a one-dimensional image of said line on said sensor; characterized in that it further comprises: - an actuating system (PR, TR1, TR2, TR3) configured to move said line of sight parallel to an optical axis of said lens (LO) or said lens placed in the object arm (L02) so as to perform a unidirectional scanning of said object, while maintaining a zero optical path difference between, on the one hand, a first path from said beam splitter to said reference mirror and back by traversing said arm reference and, secondly, a second path from said beam splitter to said observation line and back by traversing said object arm; and a processor (PR) programmed or configured to reconstitute a two-dimensional image of a section of said object to be observed, oriented parallel to said optical axis of said objective (LO) or of said objective placed in the object arm (L02), to from a plurality of one-dimensional interferometric images acquired by said sensor in correspondence of different positions of said line of observation during said unidirectional scanning.
    [0002]
    Apparatus according to claim 1 wherein said actuating system is configured to cause a relative displacement, parallel to said optical axis of said objective (LO) or said objective placed in the object arm (L02), of said object to be observed with respect to said interferometric microscope, without modifying the optical lengths of said reference arm and said object arm.
    [0003]
    An apparatus according to claim 1 wherein said actuating system is configured to move the lens (L02) in the focusing plane of which said viewing line is located and to change the optical length of said reference arm of so as to maintain zero optical path difference between said first path and said second path.
    [0004]
    4. Apparatus according to one of the preceding claims also comprising a dispersion compensation device (DCD, IM) arranged on at least one of said object arm and said reference arm, said actuating system being configured to act also on said dispersion compensating device during said unidirectional scanning.
    [0005]
    5. Apparatus according to one of the preceding claims wherein said interferometric microscope is a Linnik microscope, comprising a first objective (L01) arranged on said reference arm and a second objective (L02) arranged on said object arm, said arms of reference and object being disjoint.
    [0006]
    6. Apparatus according to one of claims 1 to 4 wherein said interferometric microscope is selected from a Michelson microscope and a Mirau microscope, comprising a single objective (LO).
    [0007]
    An optical tomography method comprising the steps of: a) providing a polychromatic light source (SLM); b) using a beam splitter (SF) to direct a first fraction of light emitted by said source along a first path, referred to as the reference path (TREF), and a second fraction of light emitted by said source along a second path, said object path (TROB); c) using a lens (L02) co-operating with a one-dimensional confocal spatial filtering system (FS) for focusing said second light fraction so as to illuminate a semi-transparent object (OBJ) to be observed along a line, called a line of observation , located in a plane of development of said objective, and for collecting the light backscattered by said object thus illuminated; d) using said objective, or other objective (L01), to focus said first light fraction on a reference mirror (MR) arranged on said reference path, and to collect the light reflected by said mirror; e) using said beam splitter (SF) to combine the light backscattered by said object with the light reflected by said mirror and direct it to a one-dimensional optical sensor (ICD); f) using said one-dimensional confocal spatial filtering system (FS) to select light from said observation line (LDO), and to form a one-dimensional image on said sensor; g) using an actuation system (PR, TR1, TR2, TR3, TRO) to move said observation line parallel to an optical axis of said objective (L02) so as to perform a unidirectional scanning of an object to observing on said object path while maintaining a zero optical path difference between said reference path and said object path; eth) using a processor (PR) to reconstruct a two-dimensional image of a section of said object to be observed, oriented parallel to said optical axis, from a plurality of one-dimensional interferometric images acquired by said sensor in correspondence of positions different from said line of observation during said unidirectional scanning.
    [0008]
    The method according to claim 7, wherein said step g) is implemented by causing a relative displacement, parallel to said optical axis, of said object to be observed with respect to said interferometric microscope without modifying the optical lengths of said reference arm and said object arm. .
    [0009]
    9. The method of claim 7 wherein said step g) is implemented by moving the objective in a focal plane which is said line of observation and by changing the optical length of said reference arm so as to maintain zero the optical path difference between said first path and said second path.
    [0010]
    10. Method according to one of claims 7 to 9 also comprising a step i) compensating for changes in the dispersion induced by the displacement of the observation line inside said object to be observed during said unidirectional scanning.
    类似技术:
    公开号 | 公开日 | 专利标题
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    同族专利:
    公开号 | 公开日
    CN105980810A|2016-09-28|
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    法律状态:
    2015-11-23| PLFP| Fee payment|Year of fee payment: 3 |
    2016-11-21| PLFP| Fee payment|Year of fee payment: 4 |
    2017-10-27| TQ| Partial transmission of property|Owner name: CENTRE NATIONAL DE LA RECHERCHE SCIENTIFIQUE, FR Effective date: 20170925 Owner name: INSTITUT D'OPTIQUE GRADUATE SCHOOL, FR Effective date: 20170925 Owner name: UNIVERSITE PARIS-SUD, FR Effective date: 20170925 |
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    优先权:
    申请号 | 申请日 | 专利标题
    FR1363234A|FR3015659B1|2013-12-20|2013-12-20|APPARATUS AND METHOD FOR OPTICAL TOMOGRAPHY|FR1363234A| FR3015659B1|2013-12-20|2013-12-20|APPARATUS AND METHOD FOR OPTICAL TOMOGRAPHY|
    PCT/EP2014/078867| WO2015092019A1|2013-12-20|2014-12-19|Optical tomography apparatus and method|
    ES14827756T| ES2800476T3|2013-12-20|2014-12-19|Optical tomography apparatus and procedure|
    AU2014368378A| AU2014368378B2|2013-12-20|2014-12-19|Optical tomography apparatus and method|
    JP2016541612A| JP6570531B2|2013-12-20|2014-12-19|Optical tomography apparatus and method|
    DK14827756.9T| DK3084345T3|2013-12-20|2014-12-19|APPARATUS AND METHOD OF OPTICAL TOMOGRAPHY|
    US15/106,164| US10317656B2|2013-12-20|2014-12-19|Optical coherence tomography apparatus and method using line confocal filtering|
    CN201480075374.8A| CN105980810B|2013-12-20|2014-12-19|Optical tomography apparatus and method|
    EP14827756.9A| EP3084345B1|2013-12-20|2014-12-19|Device and process of optical tomography|
    CA2934556A| CA2934556A1|2013-12-20|2014-12-19|Optical tomography apparatus and method|
    IL246327A| IL246327A|2013-12-20|2016-06-19|Optical tomography apparatus and method|
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