EP1576405A2 - Coherence microscope - Google Patents
Coherence microscopeInfo
- Publication number
- EP1576405A2 EP1576405A2 EP03789300A EP03789300A EP1576405A2 EP 1576405 A2 EP1576405 A2 EP 1576405A2 EP 03789300 A EP03789300 A EP 03789300A EP 03789300 A EP03789300 A EP 03789300A EP 1576405 A2 EP1576405 A2 EP 1576405A2
- Authority
- EP
- European Patent Office
- Prior art keywords
- light
- coherence
- microscope according
- coherence microscope
- fiber bundle
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Ceased
Links
Classifications
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
- G02B21/0004—Microscopes specially adapted for specific applications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B9/00—Measuring instruments characterised by the use of optical techniques
- G01B9/02—Interferometers
- G01B9/0209—Low-coherence interferometers
- G01B9/02091—Tomographic interferometers, e.g. based on optical coherence
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B2290/00—Aspects of interferometers not specifically covered by any group under G01B9/02
- G01B2290/65—Spatial scanning object beam
Definitions
- the invention relates to a coherence microscope and a method for operating such a microscope.
- a method with which sharp images of spatially extended objects can be obtained uses confocal optics for imaging.
- the concept of imaging using confocal optics is described, for example, in US 3,013,467. It is based on the fact that, for example, a pinhole light source is provided by means of a pinhole with a small hole, the light of which is focused on a point of the sample. The light reflected from this sample point is in turn focused on a point that represents an image of the sample point.
- a second pinhole is arranged at the location of this image, behind which there is a detector for detecting the reflected light. Only light coming from the focal plane is mapped to a point at the location of the second hole life and can pass through the pinhole.
- Confocal microscopes i.e. microscopes based on confocal imaging
- LSM laser scan microscopes
- the particular challenge for the corresponding microscopic screening method is to be fast, high-resolution and compatible for use in the endoscope.
- Such methods can be used to perform optical biopsies for tumor detection, for example in the gastrointestinal tract.
- a confocal laser scan microscope in connection with an endoscope is, for example, the laser described in YS Sabharwal et al., "Slit Scanning Confocal Microendoscope for High Resolution In-Vivo Imaging", Appl. Opt. 34, pages 7133-7144 (1999).
- Scan microendoscope This instrument uses a confocal diaphragm to image a laser beam onto the sample, scans the sample with the laser beam two-dimensionally (laterally) and records the scattered light reflected by the sample. In order to record a spatial, ie three-dimensional image, two-dimensional ones Layers are scanned at different depths. The depth of the plane to be recorded is adjusted by shifting the focal plane of the microscope in the sample.
- the result of this process is a so-called z-stack of two-dimensional images.
- the scans are either carried out manually (with high inaccuracy and lack of reproducibility ) or by means of miniaturized focusing devices, the high requirements Accuracy and reproducibility must be sufficient and also only be of a small size.
- the mechanical requirements for such focusing devices are very high. laser Scan microendoscopes have therefore not yet become commercial products.
- the longitudinal resolution of the laser scan microendoscope is determined by the confocal optics. Confocal imaging with the aid of an aperture ensures that only scattered light from a longitudinally narrowly limited depth range falls on the detector. The depth of this area, and thus the longitudinal resolution of the microscope, depends on the aperture of the aperture, i.e. For example, the hole of the pinhole, and in practice reaches values of typically less than 10 ⁇ m. Better longitudinal resolutions, i.e. More narrowly limited depth ranges are possible by closing the aperture further, but this is associated with a high loss of light. Disadvantages of the laser scan microendoscope are the long scanning time required to record a z-stack and a low optical sensitivity. The optical sensitivity is impaired by the generally low transmission of the optical fiber bundles of the laser scan microendoscope and by disturbing reflections on the optical surfaces.
- An alternative to imaging spatially extended objects that is not based on the principle of confocal imaging is the device described in DE 199 29 406 for performing an optical coherence tomography (OCT, Optical Coherence Tomography). It comprises a light source that emits essentially incoherent light, and a beam generating device for generating a measurement light beam and a reference light beam that is coherent with respect to a reference point in time to the measurement light beam from the incoherent light. The sample is irradiated with the measuring light beam. The light reflected by the sample is recorded and spatially overlaid with the reference light beam. Because of the temporal incoherence of the radiation, interference phenomena occur only when the optical path lengths of the measurement and reference light beam are essentially identical.
- the different optical path lengths of the reference light beam therefore lead to interference phenomena with the object reflected at different depths Measuring light.
- the different optical path lengths of the reference light beam can be related to the depth at which the reflection of the measurement light took place in the sample in order to create a depth profile of the sample.
- a disadvantage of the devices presented is that they cannot be used to perform an optical biopsy in the desired manner.
- the object of the invention is therefore to provide a device with which an optical biopsy can be implemented in a manner which is advantageous compared to the prior art. It is a further object of the invention to provide a method for operating such a device.
- the first object is achieved by a coherence microscope according to claim 1, the second object by a method according to claim 24. Further refinements of the invention are specified in the dependent claims.
- a coherence microscope comprises a light source which emits light which is incoherent in time. Any light source with a suitably short coherence length is to be regarded as a time-incoherent light source.
- the coherence microscope comprises a splitter for splitting the light emitted by the light source into measuring light, which is fed to and reflected by a sample, and reference light.
- a superimposition device for spatially superimposing the measurement light reflected from the sample with the reference light and a sensor line for detecting the light resulting from the superimposition, which is designed in such a way that it enables a readout rate of at least approx. 60 kHz.
- the overlay device has one Emission device for emitting the measurement light and the reference light, which is designed and arranged relative to the sensor line in such a way that extensive irradiation of at least part of the sensor line with superimposed light takes place and the ratio of the measurement light and the reference light from the emission device to the respective point of impact distances covered on the sensor line in the section of the sensor line irradiated with superimposed light varies.
- the coherence microscope according to the invention is based on the following considerations:
- a major obstacle to realizing an optical biopsy using the prior art described is that the acquisition times for acquiring a z-stack are long.
- a mechanical movement is also required for a standard OCT in order to obtain image information from different depths of the sample.
- the depth is determined based on the interference of a measuring beam with a reference beam.
- the depth from which the image information originates is the distance traveled from the reference beam to the detector. This distance is usually varied in that the reference beam is reflected on a movable mirror.
- the mirror position must therefore be mechanical be changed, which, like moving the optical elements in the LSM, cannot be done at the desired speed.
- the so-called line OCT described in DE 199 29406 does not require a displaceable mirror in order to determine the sample depth from which the image information originates.
- the light is emitted from the superimposition device onto the sensor line in such a way that the distance covered by the reference light beam depends on the point of incidence of the light on the sensor line.
- the sample depth in this device therefore results from the position of the point of impact of the superimposed light on the sensor line, i.e. the position of the sensor element read in each case.
- the mechanical displacement of a mirror is therefore not necessary.
- the sensor line is selected in a line OCT in such a way that the reading of the sensor line with a high read rate, i.e. 60 kHz or more, the short recording times required for the optical biopsy can be realized.
- Sensor lines with the desired readout rates and a line length between 128 and 1024 sensor elements are currently commercially available.
- the sensor line is therefore preferably a short line which does not comprise more than approximately 1000 sensor elements. In particular, if a very high readout rate is to be achieved, a very short sensor line with no more than approximately 500 sensor elements is preferably used.
- a short or very short sensor line does not necessarily have to be used. Instead, a long sensor line, ie a sensor line with more than approx. 1000 sensor elements can be used, for example one with 2048 or 4096 sensor elements.
- the high readout rate can be achieved in this case by irradiating and reading out only a part of the sensor elements, ie the length of the line used is less than its actual length. If, for example, a sensor row with 2048 sensor elements is used, only about 1000 sensor elements of the row are preferably irradiated and read. More preferably, only about 500 sensor elements are irradiated and read out.
- the short sensor line and the absence of moving parts for performing a depth scan enable the short recording times required for the optical biopsy.
- the coherence microscope according to the invention is distinguished in particular by the following points compared to the prior art:
- the sample can also be scanned along an XZ plane, i.e. can only be scanned along an X-line (so-called B-scan), the orientation and "width" of the X-direction being adjustable without the need to reposition the microscope optics, which may be integrated into an endoscope
- This enables a very fast optical biopsy, which provides the pathologist with a cut in the usual orientation.
- the width of the one-dimensional line can in particular be adapted to the desired resolution and / or the desired signal strength.
- the depth range which is accessible for measurement with the optical coherence microscope according to the invention by superimposing measurement and reference light, that is to say the depth extent of the depth profile resulting from the superimposition, is called the depth stroke.
- the depth stroke is independent of the depth resolution and is determined by the number of sensor elements in the sensor line, the wavelength of the light used and the number of sensor elements per period of the interference signal.
- the coherence microscope is in particular designed such that it has a depth stroke which corresponds at least to the depth resolution of the coherence microscope determined by the coherence length of the light emitted by the light source and at most N ⁇ / 4, where ⁇ is the wavelength of the light emitted by the light source and N is the number of Sensor elements or the sensor elements used in the sensor line.
- N ⁇ / 4 represents the greatest depth stroke for which the sensor line with N sensor elements or N sensor elements used fulfills the scanning theorem when using light of wavelength ⁇ .
- the depth stroke is typically in the range of approx. 100 ⁇ m, but it can also be below this and be, for example, 20 ⁇ m or less. In particular, it can also be in the range of the depth resolution of the coherence microscope. The lower the depth stroke, the shorter the sensor line used and thus the time it takes to take an image.
- the coherence microscope according to the invention comprises a point light source emitting measurement light and at least one confocal diaphragm.
- the point light source can also be formed by the at least one confocal diaphragm.
- microscope optics for focusing the measurement light onto the sample and for focusing the measurement light reflected from the sample onto the at least one confocal diaphragm, which may also form the point light source, or a further confocal diaphragm.
- a confocal diaphragm is not only to be understood as a perforated or slotted disc, but rather each confocally arranged optical element which has an aperture or numerical aperture.
- the aperture of the at least one confocal diaphragm is preferably selected such that the depth stroke of the coherence microscope essentially corresponds to the depth dimension of its confocal zone.
- an optical fiber is present which feeds the measuring light to the microscope optics.
- a scanning device is also preferably arranged between the optical fiber and the microscope optics.
- the at least one confocal diaphragm can be formed by the optical fiber. If a single-mode fiber is used as the optical fiber, the optical path length covered by the measuring light is fixed and known with high accuracy.
- an ordered fiber bundle is interposed between the optical fiber and the microscope optics, preferably between the scanning device and the microscope optics.
- the at least one confocal diaphragm can alternatively be formed by the optical fiber or by the fibers of the fiber bundle. Since it is not necessary to record z-stacks with the coherence microscope according to the invention, no mechanically moved elements at the distal end of the fiber are necessary. Likewise, no additional focusing devices have to be implemented at the distal end.
- the ordered fiber bundle can be integrated in an endoscope.
- the distal end of the endoscope can include magnifying optics, the numerical aperture of which is selected such that the optical resolution at the Fiber bundle end surface corresponds to the diameter of the fibers of the fiber bundle.
- a further embodiment of the coherence microscope is distinguished by the fact that a scanning device is provided for coupling measuring light into the fibers and / or for coupling measuring light reflected from the sample out of the fibers.
- a scanning device is provided for coupling measuring light into the fibers and / or for coupling measuring light reflected from the sample out of the fibers.
- an optical system is present between the scanning device and the proximal end of the ordered fiber bundle, which is designed in such a way that the light to be coupled into the fibers is slightly defocused at the proximal end of the fiber bundle. In this way, it can be ensured that each individual fiber is hit equally well in the same way.
- a scan controller can be provided which is designed to carry out an initialization in which the central position of the fibers at the proximal end of the ordered fiber bundle is determined in order to improve the coupling.
- the fibers of the ordered fiber bundle are arranged linearly next to one another at the proximal end of the fiber bundle.
- This configuration enables scanning with very high scanning frequencies.
- it enables flat scanning with only one movable scanning element.
- the scanning device can in particular have a rotatable polygon mirror.
- the described coupling and decoupling of the light at the proximal end of the fiber bundle and / or the linear arrangement of the fibers at the proximal end of the fiber bundle can be used advantageously not only in the coherence microscope according to the invention, but also in other devices in which light enters an optical fiber bundle - or to be decoupled.
- the numerical aperture and the magnification of the microscope optics of the coherence microscope according to the invention can advantageously be chosen such that the lateral resolution is approximately equal to that Corresponds to the diameter of the fibers of the ordered fiber bundle and a maximum depth stroke is achieved.
- Figure 1 shows schematically a first embodiment for the coherence microscope according to the invention.
- Figure 2 shows schematically a second embodiment of the coherence microscope according to the invention.
- FIG. 3 schematically shows the coupling in and out of light into or out of fibers of an optical fiber bundle.
- the microscope comprises a light source 1 for emitting temporally incoherent light, a splitter 3 for splitting the light into a reference beam and a measuring beam, a reference branch 5, into which the reference beam is coupled by the splitter 3 and in which it covers a defined path, one Measuring branch 7, into which the measuring beam is coupled from the splitter and via which the measuring beam is fed to the sample 13, and a detector 9 in which measuring light reflected from the sample is superimposed with reference light from the reference branch 5 and the superimposed light is detected.
- the light source 1 is a broadband light source that emits radiation that is essentially incoherent in time.
- the light source 1 is a superluminescent diode.
- other light sources can also be used, provided they emit light with a coherence length that does not exceed a predetermined value, such as a laser that emits short light pulses.
- the coherence length of the light source 1 determines the depth resolution of the optical coherence microscope.
- the microscope comprises a laser light source 15, for example a laser diode, which emits coherent radiation in the frequency range visible to the human eye.
- the laser light source 15 or the laser light emanating from it serves to be able to follow the beam path of the light emitted by the superluminescent diode 1 in the invisible area.
- the laser light is mixed in a mixer 17 with the light from the superluminescent diode 1, 90% of the mixed beam going back to the superluminescent diode 1 and 10% to the laser light source 15.
- the radiation generated by the mixer 17 is coupled by the splitter 3 to 90% into the measuring branch and to 10% into the reference branch. Other mixing ratios are also possible here.
- the reference light beam is coupled into a reference light guide 6 and fed to a mirror 19 via an optical system 18.
- the mirror 19 reflects the reference beam, which is coupled back into the reference light guide 6 after the reflection from the optics 18.
- a mixer 21 mixes the reflected reference light with the reference beam coming from the splitter 3 in a ratio of 50:50 and couples the light prepared in this way into a further reference light guide 23 leading to the detector 9, which guides the reference light beam to a beam output 25 of the reference branch 5.
- the reference light guides are preferably monomode fibers.
- the measuring light is fed via a measuring light guide 8 arranged in the measuring branch 7 to a scanning device 32, from which it is directed onto a microscope optics 28 focusing the measuring light beam onto a sample area.
- the scanning device 32 comprises a first galvanometer mirror 33 which can be pivoted about an axis for conveying an X deflection of the measurement beam and a second galvanometer mirror 35 which can be pivoted about an axis for conveying a Y deflection of the measurement beam.
- the axes about which the respective galvanometer mirrors 33, 35 can be pivoted are preferably perpendicular to one another, but can also be at any angle take each other as long as they are not parallel to each other.
- the galvanometer mirrors 33, 35 are controlled by means of a scan control (not shown) in such a way that a lateral sample area is scanned step by step. In each scanning step, the light reflected by the sample 13 is picked up by the microscope optics 28 and fed back to the measuring light guide 8 via the scanning device 32.
- the numerical aperture NA of the measuring light guide 8 represents both a point light source and a confocal diaphragm of the coherence microscope.
- the measuring light prepared in this way is coupled by the mixer 27 into a further measuring light guide 29, likewise preferably a single-mode fiber, which feeds the measuring light to the beam output 31 of the measuring branch 7.
- the reference light and the measuring light in the form of light cones 37, 39 are directed onto a CCD line 41 as the sensor line of the detector 9, which represents the sensor surface of the detector 9.
- the two beam outputs 25, 31 are arranged at a distance from one another, so that the two light cones partially overlap and illuminate at least one partial area 43 of the CCD line 41 simultaneously.
- the CCD line has 512 pixels, all of which are essentially illuminated by superimposed light. Only if the measuring light arriving at a point, ie a pixel, on the CCD line 41 has traveled the same distance as that at the same point on the CCD line 41 incoming reference light, interference phenomena occur.
- a depth within the sample 13 can be assigned to the respective point on the CCD line 41 from the known path lengths which the reference light has to cover from the beam output 25 to the respective points on the CCD line. Only measuring light which has been reflected at this depth interferes with the reference light at the assigned point on the CCD line 41.
- a read-out unit reads the CCD line and forwards the read-out data to an evaluation unit (likewise not shown), which carries out the assignment of a pixel to the sample depth from which the measurement light hitting the pixel originates. Due to the relatively small number of pixels to be read out, the CCD line can be read out at a high read rate.
- the high readout rate can also be achieved in the exemplary embodiment described if, for example, instead of a CCD line with 512 pixels, a CCD line with 1024 or more pixels is used, of which only approx. 500 are irradiated and read out with superimposed light.
- the recordings of the coherence microscope according to the invention are characterized in that a volume with an axial extent in the region of the depth of field of the confocal microscope optics is measured in a certain depth of the sample. Since the sample is scanned flat in the lateral direction, very high data rates are incurred. The entire system should therefore be designed and optimized for fast data acquisition.
- the readout rate of the CCD line required for this is estimated below:
- N is the pixel number of the CCD line
- ⁇ is the wavelength of the light source (typically 800 nm)
- P is the number of pixels per period of the Interference signal.
- the number of pixels per period can also be greater than 2; without having to use a longer line.
- the number of pixels per period can also be maintained with a lower depth stroke and the length of the CCD line can be reduced.
- the number of pixels per period should be at least 2 and advantageously be at most 4 in order to avoid unnecessarily long lines.
- the depth resolution is determined in the coherence microscope according to the invention as in the OCT by the coherence length of the light source 1.
- Each light source emits coherent light over a certain period of time, namely over the coherence time.
- Light sources with very short coherence times are considered to be incoherent light sources.
- the coherence time can be converted into a coherence length. Only those light rays whose distances covered differ by less than the coherence length can interfere with one another. The shorter the coherence length, the more precisely the path lengths of the measuring beam and reference beam must match so that they can interfere with one another, ie the path difference must be smaller than the coherence length.
- the depth resolution of the coherence microscope is preferably better than 20 ⁇ m, more preferably better than 10 ⁇ m and in particular better than 1 ⁇ m, the depth resolution depending on the desired application of the coherence microscope.
- the volume .DELTA.X, .DELTA.Y, .DELTA.Z of the scattering sample 13 can be measured with a high lateral (X, Y) and axial (Z) resolution using the coherence microscope.
- the sample 13 is scanned analogously to the confocal laser scanning microscope with the confocal microscope optics.
- the confocality is not used to increase the lateral resolution or to enable measurement in sharply defined depth ranges ( ⁇ 10 ⁇ m) as in the confocal laser scanning microscope. Instead, the confocality only serves to reduce extraneous light that comes from outside the sample area to be examined.
- the galvanometer mirrors 33, 35 can be completely or partially replaced by other scanning elements, such as, for example, rotatable polygon mirrors.
- FIG. It differs from the first exemplary embodiment only in that a focusing lens 26 and an ordered fiber bundle 100, which comprises a number of optical fibers, preferably single-mode fibers, are arranged between the scanning device 32 and the microscope optics 28.
- a focusing lens 26 and an ordered fiber bundle 100 which comprises a number of optical fibers, preferably single-mode fibers, are arranged between the scanning device 32 and the microscope optics 28.
- the measuring light is fed to the microscope optics 28 via the ordered fiber bundle 100.
- the measurement light beam is introduced into the proximal ends 106 of the optical fibers of the fiber bundle 100 via the focusing lens 26, with which the measuring light beam is focused on the input surfaces of the fibers.
- the scanning device 32 which is designed as in the first exemplary embodiment, makes it possible to align the measuring light beam onto the focusing lens 26 in such a way that it is focused on the proximal end of a selected fiber of the fiber bundle 100.
- the galvanometer mirrors 33, 35 of the scanning device 32 are controlled by means of a scan control (not shown) in such a way that the measurement light beam is introduced successively into all fibers or at least into a defined subset of all fibers of the optical fiber bundle.
- the coupling of the measurement light beam into the proximal ends of the individual fibers of the ordered fiber bundle 100 can be improved in several ways in order to achieve an optimal coupling into the individual fibers at the maximum scanning speed.
- An alternative way of improving the coupling is to control the scanning device 32 in such a way that each individual fiber of the fiber bundle 100 is optimally struck by the rastering light beam.
- the optimal setting of the scanning device is determined in an initialization step for each individual fiber.
- the proximal end 106 of the fiber bundle can be scanned in a grid that is finer than the grid that results from the arrangement of the proximal ends of the individual fibers.
- the reflections occurring at the proximal end 106 of the fiber bundle 100 during scanning are stronger if they are from a Single fibers come as if they come from the surrounding material in which the single fibers are embedded.
- the exact position of the individual fibers can therefore be determined by measuring the reflections.
- the control by the scan control then takes place on the basis of the positions determined in the initialization step. Because the reflections of the individual fibers are stronger than those of the surrounding material, it is also possible to use the reflections to synchronize the data acquisition.
- a confocal microscope optical system 28 is arranged, with which the measuring light emerging from the fibers of the fiber bundle 100 is focused on the sample 13.
- Microscope optics 28 the measurement light reflected by the sample 13 is also focused again on the distal end of the fiber of the fiber bundle 100 from which it emerged.
- the distal end of the fiber i.e. its numerical aperture represents both the point light source and the confocal aperture of the confocal optics. Also in this
- Magnification of the microscope optics are chosen so that the lateral
- Resolution of the microscope approximately corresponds to the diameter of a fiber (typically 1 to 10 ⁇ m) and a maximum axial
- the confocal aperture can also be given by the numerical aperture of the measurement light guide 8 in the second exemplary embodiment.
- the measuring light reflected by the sample 13 is fed via the fiber bundle 100 and the galvanometer mirrors 33, 35 of the scanning device 32 to a mixer 27 arranged in the measuring branch 7. This mixes the measurement light reflected by the sample 13 with the measurement beam from the splitter 3 in a ratio of 50:50.
- the measuring light prepared in this way is coupled into a measuring light guide 29, preferably a single-mode fiber, which feeds the measuring light to the beam output 31 of the measuring branch 7.
- the measurement light is superimposed on the reference light and the superimposed light is then detected as in the first exemplary embodiment.
- the optical fiber bundle 100 has the usual, almost hexagonal arrangement of the individual fibers 104 at its distal end 102. In contrast to the usual fiber bundles, however, the individual fibers 104 are arranged in a row 105 at the proximal end 106 of the fiber bundle 100. If the fiber bundle 100 comprises, for example, 50,000 individual fibers which are arranged linearly at a distance of 4 ⁇ m, the result is an extension of the line 105 of 20 cm.
- the scanning device 32 for scanning the fiber line 105 at the proximal end 106 of the fiber bundle 100 comprises a rotatable polygon mirror 108 with a number of reflecting polygon surfaces 110, the axis of rotation of which runs perpendicular to the direction of expansion of the fiber line.
- the measuring light beam is deflected from the reflecting polygon surfaces 110 in the direction of the individual fibers 104 of the line 105.
- the arrangement of the polygon mirror 108 relative to the fiber line 105 is selected such that the line 105 is scanned as often as the polygon mirror 108 has polygon surfaces 110 during a full rotation of the polygon mirror 108.
- the linear configuration of the proximal end 106 of the fiber bundle 100, i.e. the linear arrangement of the individual fibers thus enables a new type of area scan method in which the measurement light beam is deflected in one direction only for carrying out the area scan. Scanning the line by means of the polygon mirror 108 allows very high scanning frequencies.
- A-scan a complete depth profile (so-called A-scan) is recorded at every point on the XY plane without longitudinal scanning (z-scan).
- a short CCD line or a long CCD line of which only a short partial area is read out, can be used.
- the short line or the short section can for performing an A scan with a high line frequency. This enables very high measuring speeds to be achieved when performing such scans.
- the coherence microscope according to the invention enables the scanning process to be simplified. Instead of a complete XY scan, e.g. using an endoscope, the sample is scanned along an XZ plane, i.e. just scanned along an X-Line (so-called B-Scan).
- the X direction can be adjusted both in its orientation and in its "width" without the need to reposition the optics, for example the endoscope.
- This method enables the pathologist to perform a very fast optical biopsy, which is a cut in the usual orientation
- the width of the one-dimensional line can be adapted to the desired resolution and / or the desired signal strength.
- Essential areas of application of the coherence microscope according to the invention are in optical biopsy and in-vivo histology.
- the method described is suitable for external applications (examinations on the skin and mucosa), for endoscopic diagnostic methods, in particular in the gastrointestinal tract, and for ophthalmological examinations on the retina.
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Abstract
Description
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Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
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DE10260887A DE10260887A1 (en) | 2002-12-17 | 2002-12-17 | coherence microscope |
DE10260887 | 2002-12-17 | ||
PCT/EP2003/014323 WO2004055570A2 (en) | 2002-12-17 | 2003-12-16 | Coherence microscope |
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EP1576405A2 true EP1576405A2 (en) | 2005-09-21 |
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EP03789300A Ceased EP1576405A2 (en) | 2002-12-17 | 2003-12-16 | Coherence microscope |
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US (1) | US7400409B2 (en) |
EP (1) | EP1576405A2 (en) |
JP (1) | JP2006510932A (en) |
DE (1) | DE10260887A1 (en) |
WO (1) | WO2004055570A2 (en) |
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US7576865B2 (en) * | 2005-04-18 | 2009-08-18 | Zhongping Chen | Optical coherent tomographic (OCT) imaging apparatus and method using a fiber bundle |
GB2432067A (en) * | 2005-11-02 | 2007-05-09 | Oti Ophthalmic Technologies | Optical coherence tomography depth scanning with varying reference path difference over imaging array |
US7450243B2 (en) * | 2006-07-10 | 2008-11-11 | The Board Of Trustees Of The University Of Illinois | Volumetric endoscopic coherence microscopy using a coherent fiber bundle |
DE102010039289A1 (en) * | 2010-08-12 | 2012-02-16 | Leica Microsystems (Schweiz) Ag | microscope system |
JP5958027B2 (en) * | 2011-03-31 | 2016-07-27 | 株式会社ニデック | Ophthalmic laser treatment device |
JP6139516B2 (en) * | 2012-05-29 | 2017-05-31 | Hoya株式会社 | Optical coupler and confocal observation system |
US9638511B2 (en) | 2014-08-08 | 2017-05-02 | The Board Of Trustees Of The University Of Illinois | Smart phone attachment for 3-D optical coherence tomography imaging |
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JP3947275B2 (en) | 1997-08-28 | 2007-07-18 | オリンパス株式会社 | Endoscope |
US6327463B1 (en) * | 1998-05-29 | 2001-12-04 | Silicon Laboratories, Inc. | Method and apparatus for generating a variable capacitance for synthesizing high-frequency signals for wireless communications |
DE19929406A1 (en) * | 1999-06-26 | 2000-12-28 | Zeiss Carl Fa | Line OCT as an optical sensor for measurement and medical technology |
JP2001051225A (en) * | 1999-08-10 | 2001-02-23 | Asahi Optical Co Ltd | Polygon mirror, scanning optical system and endoscope device |
DE10041041A1 (en) * | 2000-08-22 | 2002-03-07 | Zeiss Carl | Interferometer device e.g. for eye surgery has beam guide which directs superimposed beam onto surfaces |
-
2002
- 2002-12-17 DE DE10260887A patent/DE10260887A1/en not_active Withdrawn
-
2003
- 2003-12-16 JP JP2004560435A patent/JP2006510932A/en active Pending
- 2003-12-16 US US10/538,587 patent/US7400409B2/en not_active Expired - Lifetime
- 2003-12-16 WO PCT/EP2003/014323 patent/WO2004055570A2/en active Application Filing
- 2003-12-16 EP EP03789300A patent/EP1576405A2/en not_active Ceased
Non-Patent Citations (1)
Title |
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See references of WO2004055570A3 * |
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US20060056784A1 (en) | 2006-03-16 |
DE10260887A1 (en) | 2004-07-01 |
US7400409B2 (en) | 2008-07-15 |
JP2006510932A (en) | 2006-03-30 |
WO2004055570A2 (en) | 2004-07-01 |
WO2004055570A3 (en) | 2004-08-26 |
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