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    • 专利摘要:
    The multi-scale retinal scanning imaging system (200) comprises, according to one example, a lighting and detection module (210) adapted for the emission of a lighting beam and the detection of a beam reemitted by the retina, a two-dimensional scanning module (231) of the illumination beam and the re-emitted beam, a first optical channel, called "wide-field" channel, and a second optical channel, called "small-field channel", for focus of the illumination beam on the retina and reception of the re-emitted beam by the retina. The "wide field" channel comprises a first optical system (205, 201) intended to combine, for example, a plane of rotation of the scanning module and the plane (17) of the entrance pupil of the eye (10). The "small field" channel comprises a wavefront correction device (250), a second optical system (257, 256, 253) for combining a rotation plane of the scanning module and the useful surface of the correction device wavefront, a third optical system, comprising at least a portion of the first optical system, allowing a conjugation between the useful surface of the correction device and the plane of the entrance pupil of the eye. The multi-scale retinal scanning imaging system further comprises at least one first optical feedback element (241) for sending the re-retracted beam to one and / or the other of the first and second imaging path, and intended to be positioned on the first imaging path, between the common part of the first and third optical systems and the scanning module, and on the second imaging path, between the common part of the first and third optical systems and the wavefront correction device.
    公开号:FR3065365A1
    申请号:FR1753568
    申请日:2017-04-25
    公开日:2018-10-26
    发明作者:Xavier Levecq
    申请人:Imagine Eyes；
    IPC主号:
    专利说明:

    (57) | _ e system (200) scanning imaging of the multi-scale retina comprises in one example an illumination and detection module (210) adapted for emitting an illumination beam and detection of a beam re-emitted by the retina, a two-dimensional scanning module (231) of the illumination beam and of the re-emitted beam, a first optical channel, called the "large field" channel, and a second optical channel, called the "small channel" -field ”, for focusing the light beam on the retina and receiving the beam re-emitted by the retina. The “wide field” path comprises a first optical system (205, 201) intended to combine, for example, a plane of rotation of the scanning module and the plane (17) of the entrance pupil of the eye (10). The "small field" channel comprises a device (250) for correcting the wavefront, a second optical system (257,256,253) intended to combine a plane of rotation of the scanner and the useful surface of the device for correcting the wavefront. wave, a third optical system, comprising at least part of the first optical system, allowing a conjugation between the useful surface of the correction device and the plane of the entrance pupil of the eye. The multi-scale retina scanning imaging system further comprises at least one first optical deflection element (241) making it possible to send the beam re-emitted by the retina to one and / or the other of the first and second imaging channel, and intended to be positioned on the first imaging channel, between the common part of the first and third optical systems and the scanner, and on the second imaging channel, between the common part of the first and third optical systems and the wavefront correction device.

    i
    MULTI-SCALE RETINAL IMAGING SYSTEM AND METHOD
    STATE OF THE ART
    Technical area
    The present description relates to a multi-scale retinal imaging system and method, more specifically to a retinal scanning system and method, making it possible to simultaneously or successively image fields of the retina of different sizes.
    State of the art
    High-resolution imaging of the retina, i.e. at the cellular level, allows early diagnosis of retinal diseases. Indeed, the first effects of retinal diseases reach the microscopic structures of the retina. The microstructures affected by the three most common and among the most serious retinal diseases (AMD for “Age-related Macular Degeneration”, glaucoma, diabetic retinopathy) are the photoreceptors, and among them the cones which vary in size from 2 and 5 μm, the micro-vessels of the retina which are the smallest vessels in the human body (approximately 6 μm in diameter), and the nerve cells which have a diameter of approximately 2 μm.
    Several laboratories offer different imaging systems for retinal imaging with cellular resolution. These different systems, also called "adaptive optics ophthalmoscopes" use different lighting and / or retina detection modules but all include an adaptive optics module for measuring the optical defects of the eye and of the system. imaging and correcting light rays from the retina and incidents on the detection system to gain resolution.
    Figure IA represents a block diagram of a retinal imaging system based on laser scanning ophthalmoscopy technology with adaptive optics or 'AOSLO' (abbreviation of the English expression 'Adaptive Optics Scanning Laser Ophthalmoscopy') , as described for example in the article by A. Roorda et al. ("Adaptive optics scanning laser ophtalmoscopy", Optics express 405, Vol. 10, N ° 9, 2002). The assembly of the AOSLO mainly comprises a lighting module 11 of the retina, a detection module 12, a scanning module 13, a correction module 14 comprising a plan for correcting the incident light rays, a wavefront analysis module 15 and an optical imaging system 16. The lighting module comprises for example a laser diode coupled to an optical fiber to form a source point and an optical lens making it possible to form from from the source point a light beam. A diaphragm of the lighting module 11 defines a pupil. The light beam is sent, for example by a set of mirrors (not shown), on the correction module 14, for example a deformable mirror, then in the scanner 13 to be directed according to a vertical and horizontal scanning in the eye 10 of a subject. The lighting beam is thus focused to form on the retina an almost punctual beam which scans the retina and the light, for example backscattered by the retina, undergoes the same optical scanning on return to be sent to the deformable mirror 14 and the module detection 12, comprising for example a confocal detection hole and a detector which can be a photomultiplier or an avalanche photodiode. A set of optical elements symbolized by the imaging system 16 participates in optically conjugating the plane of the retina and the confocal detection hole of the detector. The wavefront analysis module 15 comprises for example a Shack-Hartmann type analyzer; it receives the light backscattered by the retina and controls the deformable mirror to correct the light beam and the backscattered beam. The plane of the pupil of the lighting module, the plane of the deformable mirror and an analysis plane of the wavefront analysis module are optically conjugated with a predetermined plane 17 of the eye, for example the pupil plane of the eye.
    FIG. 1B represents a schematic diagram of an OCT type assembly (abbreviation of the Anglo-Saxon expression Optical Coherence Tomography ’) coupled with adaptive optics. Such a system is described for example in R. Zawadzki (“Adaptive-optics optical coherence tomography for high resolution and high speed 3D retinal in vivo imaging” Optics Express 8532, Vol. 13, N ° 21, 2005). The OCT is based on the use of a low coherence interferometer. This imaging technique makes it possible to produce cross-sectional images of tissue, with a resolution of a few microns. OCT's interest in ophthalmology comes from its ability to reveal tissues in vivo through other diffusing tissues. The assembly of FIG. 1B very simply takes up the main elements of an OCT type assembly. We find an arrangement similar to that of AOSLO but in which the detection module 12 is specific to OCT and notably comprises an interferometer, for example a fiber interferometer, for example of the Michelson type. The entry point of the fiber (not shown) is conjugated with the retina of the eye 10 by means of an optical conjugation system symbolized by optics 16. In comparison with AOSLO, OCT technology allows '' have a longitudinal section of the retina at the expense of the speed of acquisition.
    However, the adaptive optic ophthalmoscopes described above, if they have an excellent resolution, are limited to imaging a limited field of the retina, typically a field of a few degrees (typically less than 4 ° x4 °) ; this is due to the fact that the isoplanetic field of the eye does not allow the correction of aberrations over a much larger field with a simple adaptive optics system.
    The article by A. Dubra et al. ("First-order design of a reflective viewfinder for adaptive optics ophtalmoscopy", Optics Express, Vol. 20, N ° 24 (2012)) describes an AO SLO type adaptive optic ophthalmoscope with a particular optical arrangement, in which a system removable optical relay allows to switch between a "small-field" mode with high resolution and a "wide-field" mode, with lower resolution. Thus, the installation of the removable relay optical system makes it possible to switch to a “wide-field” optical arrangement having a greater angular enlargement at the expense of a lower pupillary enlargement. Wide-field mode allows a user to search for areas of interest in the retina. The removable relay optical system can then be removed to return to the small-field mode suitable for high-resolution retinal imaging.
    In practice, such a system is however difficult to envisage for a commercial product. Indeed, the installation of a relay optical system comprising a set of several optical conjugation elements requires readjusting the set of optical settings, which is a delicate and often long operation, unsuitable for an inexperienced user.
    Patent application WO 2016/009603 also describes an AOSLO type retinal imaging system suitable for small-field and wide-field imaging. More specifically, the system described comprises two units suitable respectively for low-resolution wide-field and high-resolution small-field imaging, the two units being separated by a separating plate. As each unit includes a lighting and detection module, associated with a specific scanning module, as well as its own imaging system, a user can have access to both small-field and wide-field imaging without any adjustment and simultaneously. This system, however, involves doubling the lighting and detection modules as well as the scanning modules for the formation of large-field and small-field units, which is not satisfactory.
    An object of the present description is to propose a multi-scale retina scanning imaging system, that is to say adapted to wide-field and small-field imaging which does not have the limitations of prior art. More specifically, an object of the present description is to propose a multi-scale retina scanning imaging system in which small-field imaging and large-field imaging can be carried out with the same lighting module. and detection and the same scanner, but which can be used without difficulty by an inexperienced user.
    SUMMARY OF THE INVENTION
    According to a first aspect, the present description relates to a multi-scale retinal scanning imaging system comprising:
    at least a first lighting and detection module adapted for the emission of at least a first lighting beam with a diameter of given dimension and the detection of at least a first beam re-emitted by the retina;
    at least a first two-dimensional scanner of the at least one first light beam and the at least one re-emitted first beam; a first optical channel, called the "wide field" channel, for focusing the at least one first light beam on the retina and receiving the at least one first beam re-emitted by the retina, comprising:
    o a first optical system with a first magnification, intended to conjugate a plane located near a plane of rotation of the at least one first scanning module and the plane of the entrance pupil of the eye;
    a second optical channel, called the “small field” channel, for focusing the at least one first light beam on the retina and receiving the at least one first beam re-emitted by the retina, comprising:
    o a wavefront correction device having a useful surface of given size;
    o a second optical system with a second magnification intended to combine a plane located near a plane of rotation of the at least one first scanning module and the useful surface of the wavefront correction device, o a third optical system with a third magnification, comprising at least part of the first optical system, allowing a conjugation between said useful surface of the correction device and the plane of the entrance pupil of the eye;
    at least one first optical deflection element, at least partially reflecting, making it possible to send the at least one first beam re-emitted by the retina on one and / or the other of the first and second imaging channels, and intended for be positioned on the first imaging channel, between the common part of the first and third optical systems and the at least one first scanner, and on the second imaging channel, between the common part of the first and third optical systems and the wavefront correction device.
    The applicant has shown that an imaging system thus described allows small-field and / or wide-field imaging with a single lighting and detection module and a single scanning module for the two channels, and very simple to use. 'use. Indeed, the particular arrangement of said first optical return element in the system makes it possible to define the pupillary magnification specific to each channel by fixed elements of the system. No adjustment on optical elements with optical power is therefore necessary when switching from one imaging channel to another.
    Said at least one first optical return element can be a simple removable reflecting surface, for example a removable mirror, making it possible to switch between one and the other of the first and second imaging channels.
    Said at least a first optical deflection element can also be a dichroic plate, making it possible to send the at least one first beam re-emitted by the retina on one of said first and second imaging channels and to send at least a second beam re-emitted by the retina, with a wavelength different from that of said at least one first beam re-emitted by the retina, on the other imaging channel. This configuration requires working with several beams of different wavelengths (and therefore two sources and potentially two detectors in the lighting and detection module) but has the advantage of allowing simultaneous small-field and large-field imaging. with a single scanner. The images in the two fields, small-field and large-field, can therefore be taken simultaneously, by the same scanner; they therefore have the same angular reference, which makes the co-location of the two images immediate.
    According to one or more exemplary embodiments, the first optical deflection element, for example a removable reflecting surface or a dichroic strip, also makes it possible to send the at least one first light beam onto one and / or the other of the first and second imaging paths. In this case, only an optical return element is necessary in the imaging system, which makes it particularly simple to implement.
    According to one or more exemplary embodiments, a second optical deflection element, for example a second removable reflecting surface or a dichroic strip, makes it possible to send the at least one first light beam on one and / or the other. first and second imaging channels.
    According to one or more exemplary embodiments, said first lighting and detection module is suitable for imaging of the retina of the AOSLO type. Said first lighting and detection module in this example comprises at least one point light source and at least one confocal detection system.
    According to one or more exemplary embodiments, said first lighting and detection module is suitable for imaging of the retina of the OCT type. Said first lighting and detection module comprises at least one point light source and at least one interferometer for detection.
    According to one or more exemplary embodiments, the multi-scale retina scanning imaging system comprises a first lighting and detection module and a second lighting and detection module, each associated with a scanning module. For example, the first lighting and detection module is suitable for imaging of the retina of the AOSLO type and the second lighting and detection module is suitable for imaging of the retina of the OCT type, making it possible to benefit from two types of imagery, with the same system, either in small-field mode or in wide-field mode.
    Thus, according to one or more exemplary embodiments, the multi-scale retina scanning imaging system further comprises:
    a second lighting and detection module adapted for the emission of at least one second lighting beam with a diameter of given dimension and the detection of at least one second beam re-emitted by the retina;
    a second two-dimensional scanner of the at least one second light beam and the at least one second re-emitted beam.
    According to one or more exemplary embodiments, the multi-scale retina scanning imaging system further comprises a wavefront analysis module adapted for the analysis of at least part of the optical defects of a beam re-emitted by the retina and sent to the second imaging channel.
    In the following description, the term "optical defects" means the disturbances to which the light rays undergo between the retina and a detector of a lighting or detection module. These defects include for example the defects brought by the optical system of the eye but also by at least part of the optics of the small-field imaging channel.
    According to one or more exemplary embodiments, the wavefront analysis module comprises a Shack-Hartmann type analyzer. Such a device makes it possible to analyze, with respect to nominal directions, the variation of the directions of the light rays after having passed through the optical system marred by optical defects. Such a device performs this measurement thanks, for example, to the arrangement of a matrix detector in the focal plane of a microlens array. The variations thus measured can be used directly for checking the wavefront correction device.
    According to one or more exemplary embodiments, the multiscale scanning imaging system further comprises a lighting module suitable for the emission of a lighting beam from the retina for the measurement of the wavefront.
    According to one or more exemplary embodiments, the wavefront correction device comprises a deformable mirror, a spatial light modulator with liquid crystal (SLM) (spatial light modulator), a MEMs (micro electromechanical systems), a lens multi actuator liquid. The wavefront correction device can be controlled by a wavefront analysis module, for example in a closed loop servo configuration, or be controlled using algorithms based on a quality criterion retinal images acquired by the lighting and detection module.
    According to a second aspect, the present description relates to a scanning imaging method of the retina by means of an imaging system according to the first aspect.
    According to one or more exemplary embodiments, said at least one first optical deflection element is a removable reflecting surface and the method comprises removing said at least one first optical deflection element to switch from one of said first and second pathways. imaging to the other imaging path.
    According to one or more exemplary embodiments, said reflecting surface is inserted or removed in an insertion or withdrawal movement parallel to the reflecting surface; this avoids that a positioning error when stopping the mirror could affect the alignment of a beam reflected by said reflecting surface.
    According to one or more exemplary embodiments, said at least one first optical return element is a dichroic plate and the method comprises sending the at least one first beam re-emitted by the retina on one of said first and second imaging channels. and sending at least one second beam re-emitted by the retina on the other imaging channel, said first and second beams re-emitted by the retina having different wavelengths.
    BRIEF DESCRIPTION OF THE DRAWINGS
    Other advantages and characteristics of the invention will appear on reading the description, illustrated by the following figures:
    - FIGS. IA and IB (already described), block diagrams of scanning retina imaging systems known from the prior art;
    - FIGS. 2A - 2C, diagrams illustrating the operation of a first embodiment of a retinal scanning imaging system according to the present description;
    - FIGS. 3A, 3B, diagrams showing examples of lighting and detection modules, suitable for imaging of the retina of the AO SLO type and of the OCT type, respectively;
    - FIG. 4, a diagram showing the operation of another exemplary embodiment of a retinal scanning imaging system according to the present description;
    - FIGS 5A - 5B, diagrams illustrating the operation of another embodiment of a scanning imaging system of the retina according to the present description.
    For the sake of consistency, identical elements are identified by the same references in the different figures.
    DETAILED DESCRIPTION
    FIGS 2A to 2C illustrate the operation of a first embodiment of a multi-scale retinal scanning imaging system.
    In this example, a simple removable optical return element 241, for example a removable plane mirror reflecting at the wavelengths of the different light beams and beams re-emitted by the retina, makes it possible to switch between a wide-field imaging channel. (FIG. 2A) and a small-field imaging channel (FIG. 2B). FIG. 2C illustrates the analysis of optical defects in the case of small-field imaging.
    The imaging system 200 shown in FIGS 2A - 2C comprises a first lighting and detection module 210 and a second lighting and detection module 220. Examples of such lighting and detection modules will be described more in detail with reference to FIGS 3A -3B. Each lighting and detection module is suitable for the emission of one or more light beams and the detection of one or more beams re-emitted by the retina after illumination by said light beams. A beam re-emitted by the retina can be a back-scattered beam at the same wavelength as that of the lighting beam, or re-emitted at a different wavelength when the lighting beam induces for example a fluorescence mechanism at the level retina.
    For example, a light and detection module can be adapted for the emission of two light beams from the retina, at different wavelengths, as will be described later with reference to FIG. 4. Alternatively, as in the case for example of FIGS. 2A - 2C, the lighting and detection modules are suitable for the emission of an illumination beam at a given length and the detection of a beam re-emitted by the retina, at this same wavelength, or at a different wavelength in the case of re-emission of fluorescence by the retina.
    The imaging system 200 further comprises, associated with each of the lighting and detection modules 210, 220, a two-dimensional scanning module referenced respectively 231, 232.
    Each two-dimensional scanning module is suitable for scanning the light beam emitted by the lighting and detection module and scanning the beam emitted by the retina to be sent to the lighting and detection module. A scanning module or “scanner” comprises for example a combination of mirrors motorized by means of galvanometric motors or a combination of MEMS mirror (with one axis) or a MEMS mirror with two axes. For each scanner, a rotation plane can be defined which includes the axis of rotation; a plane of rotation is then confused with the plane of the mirror. In the case where two separate mirrors are used to carry out the two rotations, it is advantageous that the planes of rotation of these two mirrors are conjugated optically, for example by means of an optical system which conjugates the two planes. In the case where the two-dimensional scanner comprises two separate and non-conjugated scanning mirrors, it is advantageous that they are located at the shortest possible distance from each other.
    In the example of FGS 2A - 2C, the light beams emitted respectively by the lighting and detection modules 210, 220 and scanned by the scanning modules 231 and 232 respectively are combined and sent to the imaging channels by means of a partially reflecting plate 206, for example a dichroic plate if the light beams have different wavelengths. The same partially reflective plate separates the beams re-emitted by the retina towards each of the lighting and detection modules.
    According to the present description, the imaging system 200 comprises a first optical path, called the "wide-field" path, and a second optical path, called the "small-field" path, either of which can be activated, in the example of FIGS. 2A - 2C, thanks to the installation or removal of the removable reflecting surface 241; and each of said channels allowing the focusing on the retina of the light beam coming from the lighting and detection module and the reception of the beam re-emitted by the retina.
    FIG. 2A represents the case where the wide-field channel is activated. To do this, in this example, the removable reflecting surface 241 is put in place. As it can be a simple mirror, for example a plane mirror, no adjustment is necessary. For example, the mirror is inserted in an insertion movement parallel to the reflecting surface, thus avoiding a positioning error when the mirror is stopped could affect the alignment of a beam reflected by said surface. reflective.
    The wide-field path comprises a first optical system, in this example comprising a set of optical elements 201, 205, and having a first magnification gi. The first optical system is intended to combine a plane positioned close to a plane of rotation of the scanner and the plane 17 of the pupil of the eye 10 of a patient.
    In the case where the two-dimensional scanner comprises a mirror with a plane of rotation, or two mirrors optically conjugated with each other, the first optical system may conjugate the one or one of said planes of rotation with the plane 17 of the entrance pupil of the eye 10. In the case where the two-dimensional scanning module comprises two distinct and non-conjugated scanning mirrors, the first optical system may conjugate a plane located between the two mirrors, for example a plane located at one median distance of the two mirrors, with the plane 17 of the entrance pupil of the eye 10.
    The wide-field path further comprises a set of optical deflection elements, in this example 204, 203, 202, for directing the light beam towards the eye 10.
    Thus, in the case of “wide-field” imaging, the diameter Φει of the exit pupil of the optical imaging system at the plane 17 of the pupil of the eye is given by:
    Φει - gi Φ ^ ι (1)
    The “optical imaging system” is defined by the set of imaging elements between the entrance pupil of the eye and a detector of a lighting and detection module and <t> cc i is the diameter of the light beam at the output of the scanner.
    Note that in the case where there are two lighting and detection modules, there may be lighting beams of different diameters and therefore different Φει values, although we will try to make this difference minimal.
    The "pupil" of an optical system is understood to mean the smallest opening that limits the entry or propagation of light rays into the system. This opening may be real in the case where a physical diaphragm, pupil of the optical system considered, limits the entry of light or virtual rays in the case where this opening is an image of the physical pupil of the optical system which is located inside the optical system and which is formed for example by a diaphragm. Thus, in the case where the exit pupil of the optical imaging system is positioned in the pupillary plane of the eye or in a plane situated near the latter, said exit pupil is virtual, image of a diaphragm located inside said optical imaging system.
    FIG. 2B represents the case where the small-field path is activated. To do this, in this example, the removable reflecting surface 241 is removed.
    The “small field” channel comprises a wavefront correction device 250 having a useful surface 251 of given size, a second optical system, intended to combine a plane located near a plane of rotation of the scanner and the useful surface 251 and having a second magnification g2. The second optical system includes in the example of FIGS. 2A - 2C a set of optical elements 257, 256, 253.
    As for the wide-field channel, in the case where the two-dimensional scanner comprises a mirror with a plane of rotation, or two mirrors optically conjugated with each other, the second optical system may conjugate the one or one of said planes of rotation with the useful surface 251 of the wavefront correction device. In the case where the two-dimensional scanning module comprises two distinct and non-conjugated scanning mirrors, the second optical system may combine a plane located between the two mirrors, for example a plane located at a median distance from the two mirrors, with the useful surface 251 of the forehead correction device.
    The “small field” path further comprises a third optical system adapted to combine the useful surface 251 of the correction device and the plane 17 of the eye entrance pupil 10, having a third magnification g3. The third optical system includes at least a portion of the first optical system; in the example of FIGS 2A - 2C, the third optical system comprises all the optical elements of the first optical system, namely the optical elements 205, 201; the third optical system is therefore confused with the first optical system (g3 = gi).
    The small-field path also includes a set of optical deflection elements, in this example 255, 254, 252, for directing the light beam towards the eye 10 of a patient.
    Thus, in the case of “small-field” imagery, the diameter Φε2 of the exit pupil of the optical imaging system at the plane 17 of the pupil of the eye, is given by:
    Φε2 = g3 ΦΰΜ (2)
    Where Φομ is the smaller of the two diameters between the diameter of the illuminated surface of the wavefront correction device and the diameter of the useful surface of the wavefront correction device, and checks:
    Φομ = g2 Φ ^ ι (3)
    In general, for a system sized to optimize the resolution, Φομ will be the diameter of the useful surface of the wavefront correction device.
    Thus, this results in the following magnification between the diameter of the light beam leaving the scanning module and the diameter Φε2 of the exit pupil of the optical imaging system at the plane 17 of the pupil of the eye:
    Φε2 = g3. g2 Φ ^ ι (4)
    From equations (1) and (4), it can be seen that it is thus possible to change the dimension of the diameter of the exit pupil of the optical imaging system at the plane 17 of the pupil of the eye by a simple installation or removal of the reflecting surface 241.
    With a larger pupil (FIG. 2B), for the same scanning angle at the level of the scanning mirror (s), the field is smaller but the resolution greater. Indeed, the resolution limit is directly proportional to the size of the pupil. On the other hand, the scanning angle at the level of the pupil entering the eye is equal to the scanning angle at the level of the scanning mirror (s) multiplied by the magnification of the optical system between the mirror (s). scan and the entrance pupil in the eye. Magnification is the opposite of magnification. Therefore if the entrance pupil is larger by a factor X in the case of small-field imaging compared to the entrance pupil in the eye of the case of wide-field imaging, the scanning angle at the entrance pupil to the eye for small-field imaging is smaller by the same X-factor as the scanning angle at the entrance pupil to the eye for wide-field imaging (for the same physical scanning angle of the scanning mirror (s)). A reduction in the scanning angle at the level of the pupil entering the eye for small-field imaging is entirely acceptable because when looking for high resolution (case of small-field imaging ), the isoplanetic field of the eye anyway reduces the field of the image to a few degrees (typically 4 ° x4 °).
    In the example of FIGS 2A - 2C, the imaging system 200 further comprises a wavefront analysis module suitable for analyzing the optical defects of a beam re-emitted by the retina and sent to the second imaging route. FIG. 2C more particularly illustrates the path of the optical beams for the analysis of optical faults (analysis path).
    This involves analyzing disturbances that the light rays undergo between the retina and a detector of the lighting and detection module, and more precisely, between the retina and an analysis plane of the front analyzer. wave. Optical defects within the meaning of this description therefore include defects provided by the optical system of the eye but also by the part of the optical imaging system common with the analysis path. Note, however, that any defects in the analysis pathway may have been measured during manufacturing and the correction may take this into account. The wavefront analysis module comprises for example a Shack-Hartmann type analyzer 270 (HASO® 32-eye Imagine Eyes®), comprising an analysis plane 271 formed of a set of microlenses and a detector arranged in the focal plane of the microlenses.
    In the example of FIGS 2A - 2C, a partially reflecting plate 258 makes it possible to take a beam re-emitted by the retina to send it to the module of analysis of the wave front. The optical defects module includes in this example a set of optical elements 265, 267 making it possible to combine the analysis plane 271 with the plane 17 of the entrance pupil of the imaging system as well as a mirror 266. According to an exemplary embodiment, the blade 258 is a dichroic blade and the analysis beam has a different wavelength from the other beam (s) re-emitted by the retina for imaging, as described by after.
    A computer (not shown) makes it possible to determine the optical defects of the system and to send a correction command to the correction device 250, for example a deformable mirror of the Mirao 52-e Imagine Eyes® type. Advantageously, the computer, associated with the Shack-Hartmann, determines with respect to nominal directions the variation of the directions of the light rays after having passed through the optical system marred by optical defects. The variations thus measured can be directly exploited for the control of the deformable mirror. The plane of the deformable mirror is also optically conjugated with the plane 17 of the entrance pupil of the imaging system.
    Other wavefront correction devices can be used, such as a spatial light modulator (SLM) or a MEMs or a multi-actuator liquid lens.
    In the example of FIGS. 2A - 2C, the multiscale scanning imaging system further comprises an illumination module adapted for the emission of an illumination beam from the retina for the measurement of optical defects.
    The lighting module in this example comprises a source 261 of retinal lighting intended for the analysis of optical defects of the imaging system. The source 261 makes it possible to form a secondary source point on the retina of the subject's eye. For example, the central wavelength of the light source 261 for the analysis of optical defects is 750 nm, such a wavelength being comfortable for the subject and as close as possible to the length (s) ( s) imaging wave. Preferably the wavelength of the source 261 is different from that of the light sources of the lighting and detection modules 210, 220 for reasons of separation of the optical paths between the measurement of the optical defects and the imaging of the retina. . The source 261 is for example a laser diode or more advantageously an SLED super-luminescent diode. A separating plate 202 makes it possible to send the light beams of illumination from the retina to the subject's eye 10 for imaging and for analyzing optical defects. A set of optical elements 262, 263, 264 make it possible to form from the light source 261 a beam intended to be focused on the retina. The lens 263 can be a variable power liquid lens (of the Varioptic® Artic® 25H0 type for example) to compensate for the ametropia of the eye examined.
    FIGS. 3A and 3B show examples of lighting and detection modules, suitable for imaging of the retina of the AO SLO type and of the OCT type, respectively.
    FIG. 3A represents a lighting and detection module 210 of known type, suitable for imaging of the retina respectively of the AO SLO type, and a two-dimensional scanning module 231 for scanning a light beam emitted by the module 210 and of a beam re-emitted by the retina after illumination by said illumination beam. The module 210 in this example comprises a light source 211, for example a laser diode coupled to an optical fiber to form a source point and an optical lens 212 making it possible to form from the source point an illumination beam of diameter <E> ec i given. The lighting and detection module 210 also includes a confocal detection hole 215 through which the beam re-emitted by the retina is focused by means of an optic 214. The module 210 also comprises a detector 216 , for example a photomultiplier or an avalanche photodiode, connected to a signal processing unit
    217, itself connected to a screen 218. A partially reflective blade 213 makes it possible to separate the beams on transmission and on reception.
    FIG. 3B represents a lighting and detection module 220 of known type, suitable for imaging the retina of the OCT type respectively, and a two-dimensional scanning module 232 for scanning a light beam emitted by the module 220 and of a beam re-emitted by the retina after illumination by said illumination beam. The module 220 in this example comprises a light source 221 with low temporal coherence, for example a light source of SLED type and a detection module formed by an interferometer, for example a fiber interferometer, for example of the Michelson type, comprising in this example a fiber-reinforced reference arm with a reflection element 225 and an optic 224. A coupler 223 receives the beams coming from the fibers 222-1, 222-2, 222-3 respectively coming from the source, the reference arm and the retina for the formation of interference on a detector 226, for example a photomultiplier or an avalanche photodiode; The module 220 also includes a signal processing unit 227, itself connected to a screen 228.
    FIG. 4 illustrates a diagram of the operation of another exemplary embodiment of an imaging system 400 with scanning the retina according to the present description.
    In this example, the optical return element allowing the separation of the small-field and large-field channels is not a removable reflecting surface but a dichroic plate 441. All of the elements identical to those described with reference to FIGS. 2A - 2C are indicated with identical references are not described again.
    To facilitate understanding of the figure, it has been assumed in this example that only a lighting and detection module 410 is active, for example a lighting and detection module suitable for imaging of the retina respectively of the AO SLO type. .
    In this example, the lighting and detection module 410 comprises a submodule 410a for lighting and detection at a first wavelength and submodule 410 B for lighting and detection at a second wavelength wave, different from the first wavelength.
    In this example, the light beam at the first wavelength, illustrated in bold line, and emitted by the sub-module 410a, is scanned by the scanning module 231 then directly reflected on the wide-field path comprising the first optical system 205, 201 by means of the dichroic blade 441.
    The beam of illumination at the second wavelength, illustrated in thin line, and emitted by the sub-module 410 B , is also scanned by the scanning module 231 then transmitted by means of the dichroic blade 441 towards the small channel -field comprising the second (257,
    256, 253) and third (205, 201) optical systems.
    A partially reflecting plate 413 makes it possible to send the light beams to the retina of the eye and to send the beams re-emitted by the illuminated retina respectively to each of the sub-modules.
    This configuration allows simultaneous access to the small-field and wide-field imaging channels with the same scanner 231 and therefore allows very easy and very reliable collocation of the two images. The ratio between the angular size of the two fields is equal to the ratio between the sizes of the diameters of the pupils of the two beams at the level of the pupil of the eye.
    FIGS. 5A - 5B illustrate the operation of another exemplary embodiment of a scanning imaging system of the retina 500 according to the present description.
    In this example, a first optical return element 541, at least partially reflecting, makes it possible to send a first beam re-emitted by the retina on one and / or the other of the first and second imaging channels, and a second return optical element 542 makes it possible to send the at least one first light beam on one and / or the other of the first and second imaging channels.
    Again, all of the elements identical to those described with reference to FIGS. 2A - 2C are indicated with identical references are not described again.
    For example, the first and second return optical elements 541, 542 are integral removable reflecting surfaces. Alternatively, the first and second optical return elements 541, 542 can be dichroic blades, as described previously with reference to FIG. 4.
    Thus, FIG. 5A illustrates the operation of the retina imaging system when the wide-field optical channel is activated, with the first optical system 205, 201, which is obtained in this example when the return elements 541, 542 are removed. FIG. 5B illustrates the operation of the retina imaging system when the petitchamp optical pathway is activated, which is obtained in this example when the return elements 541, 542 are put in place. This particular configuration makes it possible in particular to limit the number of reflective elements in the wide-field channel.
    The “small field” channel comprises, as before, a wavefront correction device 250 having a useful surface 251 of given size, and a second optical system, intended to combine a plane of rotation of the scanner and the surface useful 251 and having a second magnification g 2 . The second optical system comprises in the example of FIGS. 5A - 5B a set of optical elements 557, 556, 553.
    The “small field” path also comprises, as before, a third optical system adapted to combine the useful surface 251 of the correction device and the plane 17 of the entrance pupil of the eye 10, having a third magnification g 3 . The third optical system in this example comprises the optical elements 205, 201 forming the first optical system. The small-field path also comprises a set of optical return elements, in this example 555, 554, 552, for directing the light beam towards the eye 10 of a patient. A partially-reflecting plate 558, for example a dichroic plate, makes it possible, as before, to deflect the beam re-emitted by the retina at the wavelength from the analysis source 261 towards the module for analyzing optical defects.
    Although described through a certain number of detailed exemplary embodiments, the retinal imaging device and the method according to the invention include different variants, modifications and improvements which will be obvious to those skilled in the art, being understood that these different variants, modifications and improvements form part of the scope of the invention, as defined by the claims which follow.
    In particular, only one lighting and detection module can be used, in which case the partially reflective plate 206 illustrated in FIGS 2A - 2C, 4, 5A - 5B is no longer necessary. In addition, examples of retinal scanning imaging systems have been described with a lighting and detection module suitable for retinal imaging of the AOSLO or OCT type. The present description can generally be applied to any device for scanning the retina with adaptive optics.
    The retina lighting module for the analysis of optical faults is optional, the analysis of faults can be carried out on a beam re-emitted by the retina, resulting from the lighting by one of the lighting modules and detection 210, 220. It is also possible to dispense with a wavefront analysis module, for example by implementing a correction method which is based on a quality criterion of the acquired images, although the use of a wavefront analysis module is preferable for reasons of servo speed.
    In addition, the optical systems have been shown for illustrative purposes and can be modified according to the specific needs of the application; for example, refractive optical systems can be replaced by reflective optical systems.
    Finally, in the example of FIGS 2A - 2C, the "wide-field" imaging channel is activated when the deflection element (s) are in place and the "petitchamp" imaging channel is activated when the deflection element (s) are removed but the optical system could easily be designed so that it is the reverse (as in the case of FIGS 5A 5B).
    权利要求:
    Claims (13)
    [1" id="c-fr-0001]
    1. Multi-scale retina scanning imaging system (200) comprising:
    at least a first lighting and detection module (210) adapted for the emission of at least a first lighting beam with a diameter of given dimension (Φ eci) and the detection of at least a first re-emitted beam by the retina;
    at least a first two-dimensional scanner (231) of the at least one first light beam and the at least one re-emitted first beam; a first optical channel, called the "wide field" channel, for focusing the at least one first light beam on the retina and receiving the at least one first beam re-emitted by the retina, comprising:
    o a first optical system (205, 201) with a first magnification (gi), intended to combine a plane located near a plane of rotation of the at least one scanning module and the plane (17) of the pupil of eye entry (10);
    a second optical channel, called the “small field” channel, for focusing the at least one first light beam on the retina and receiving the at least one first beam re-emitted by the retina, comprising:
    o a device (250) for wavefront correction having a useful surface (251) of given dimension (®dm);
    a second optical system (257, 256, 253) with a second magnification (g2) intended to combine a plane located near a plane of rotation of the at least one first scanner and the useful surface of the correction device for wave front, o a third optical system with a third magnification (g3), comprising at least part of the first optical system, allowing a conjugation between said useful surface (251) of the correction device and the plane (17) of the entrance pupil of the eye (10);
    at least one first optical deflection element (241, 242), at least partially reflecting, making it possible to send the at least one first beam re-emitted by the retina on one and / or the other of the first and second channels of imaging, and intended to be positioned on the first imaging channel, between the common part (201, 205) of the first and third optical systems and the at least one first scanner (210), and on the second imaging channel imaging, between the common part of the first and third optical systems and the wavefront correction device.
    [2" id="c-fr-0002]
    2. A multi-scale scanning imaging system according to claim 1, in which said first optical deflection element (241, 441) is adapted to send the at least one first beam re-emitted by the retina onto one and / or the other of the first and second imaging channels and to further send the at least one first light beam on one and / or the other of the first and second imaging channels.
    [3" id="c-fr-0003]
    3. A multi-scale scanning imaging system according to claim 1, further comprising a second optical deflection element (542), adapted to send the at least one first light beam on one and / or the other of the first and second imaging paths.
    [4" id="c-fr-0004]
    4. Multiscale scanning imaging system according to one of the preceding claims, in which said at least one first optical deflection element is a removable reflecting surface, making it possible to switch between one of the first and second pathways. imagery and the other.
    [5" id="c-fr-0005]
    5. Multiscale scanning imaging system according to one of the preceding claims, in which said at least one first optical deflection element is a dichroic plate, making it possible to send the at least one first beam re-emitted by the retina onto one of said first and second imaging channels and to send at least one second beam re-emitted by the retina, of wavelength different from that of said at least one first beam re-emitted by the retina, on the other channel d 'imagery.
    [6" id="c-fr-0006]
    6. Multi-scale scanning imaging system according to one of the preceding claims, in which said at least one first lighting and detection module comprises at least one point light source (211) and at least one detection system confocal, suitable for AOSLO type retinal imaging.
    [7" id="c-fr-0007]
    7. Multi-scale scanning imaging system according to one of the preceding claims, in which said at least one first lighting and detection module comprises at least one point light source (221) and at least one interferometer, suitable for OCT-type retinal imaging.
    [8" id="c-fr-0008]
    8. Multiscale scanning imaging system according to one of the preceding claims, further comprising:
    a second lighting and detection module (220) adapted for the emission of at least one second lighting beam with a diameter of given dimension and the detection of at least one second beam re-emitted by the retina;
    a second two-dimensional scanner (232) of the at least one second light beam and the at least one second re-emitted beam.
    [9" id="c-fr-0009]
    9. Multiscale scanning imaging system according to one of the preceding claims, further comprising a wavefront analysis module, suitable for the analysis of at least part of the optical defects of a beam re-emitted by the retina and sent to the second imaging channel.
    [10" id="c-fr-0010]
    10. Multiscale scanning imaging system according to claim 9, in which the wavefront analysis module comprises a ShackHartmann type analyzer.
    [11" id="c-fr-0011]
    11. Multiscale scanning imaging system according to claim 9, further comprising a lighting module adapted for the emission of an illumination beam from the retina for the measurement. optical defects.
    [12" id="c-fr-0012]
    12. A method of imaging the retina by means of an imaging system according to any one of the preceding claims, wherein
    - Said at least a first optical deflection element is a removable reflecting surface; and the method includes:
    removing said at least one first return optical element to switch from one of said first and second imaging channels to the other imaging channel.
    [13" id="c-fr-0013]
    13. A method of imaging the retina by means of an imaging system according to any one of claims 1 to 11, wherein said at least one first optical deflection element is a dichroic slide; the method comprising:
    sending the at least one first beam re-emitted by the retina on one of said first and second imaging channels and sending at least one second beam re-emitted by the retina on the other imaging channel, said first and second beams re-emitted by the retina having different wavelengths.
    1/8
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    法律状态:
    2018-04-24| PLFP| Fee payment|Year of fee payment: 2 |
    2018-10-26| PLSC| Publication of the preliminary search report|Effective date: 20181026 |
    2019-04-23| PLFP| Fee payment|Year of fee payment: 3 |
    2020-04-23| PLFP| Fee payment|Year of fee payment: 4 |
    2021-04-20| PLFP| Fee payment|Year of fee payment: 5 |
    优先权:
    申请号 | 申请日 | 专利标题
    FR1753568|2017-04-25|
    FR1753568A|FR3065365B1|2017-04-25|2017-04-25|MULTI-SCALE RETINAL IMAGING SYSTEM AND METHOD|FR1753568A| FR3065365B1|2017-04-25|2017-04-25|MULTI-SCALE RETINAL IMAGING SYSTEM AND METHOD|
    US16/608,393| US20200178797A1|2017-04-25|2018-04-18|System and method for multi-scale retinal imaging|
    JP2019558403A| JP2020517375A|2017-04-25|2018-04-18|Multi-scale scanning imaging system and multi-scale scanning imaging method|
    CN201880042821.8A| CN110831489A|2017-04-25|2018-04-18|System and method for multi-scale retinal imaging|
    EP18722414.2A| EP3614904A1|2017-04-25|2018-04-18|System and method for multi-scale retinal imaging|
    PCT/EP2018/059854| WO2018197288A1|2017-04-25|2018-04-18|System and method for multi-scale retinal imaging|
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