WO2004043245A1 - A method of fast imaging of objects by means of spectral optical coherence tomography - Google Patents
A method of fast imaging of objects by means of spectral optical coherence tomography Download PDFInfo
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- WO2004043245A1 WO2004043245A1 PCT/PL2003/000118 PL0300118W WO2004043245A1 WO 2004043245 A1 WO2004043245 A1 WO 2004043245A1 PL 0300118 W PL0300118 W PL 0300118W WO 2004043245 A1 WO2004043245 A1 WO 2004043245A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
- A61B3/1225—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes using coherent radiation
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
- G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
Definitions
- the subject of the invention is a method of fast imaging of objects by means of spectral optical coherence tomography using partially coherent light and a matrix of photo-detectors with memory, specially suitable for medical imaging.
- One previously known method of imaging of cross-sections of transparent and semi-transparent objects by means of optical coherence tomography using partially coherent light consists in recovering information on the structure of the object along the line of propagation of the penetrating probe beam from the interference signal, and information on consecutive strips in a cross-section of the object by shifting the probe beam perpendicularly to its direction of propagation.
- This method is implemented using a Michelson interferometer with a light source of high spatial coherence but low temporal coherence, and by placing the sample to be examined in one arm of the interferometer and the translatable reference mirror in the other arm.
- the interference signal originating in the interferometer during translation of the reference mirror is registered by a photodiode whose output is filtered with an analog band filter.
- the signal is then digitized and transferred to a computer. This complete sequence is repeated sequentially for consecutive strips in the cross-section of the image.
- the other known method of spectral optical coherence tomography using partially coherent light consists in recording spectral fringes with the spectrograph without translation of the reference mirror. In this method many photo-detectors simultaneously registering the whole spectrum are employed. Information on the axial structure of the object is recovered from the spectral signal by means of numerical Fourier transform.
- the inconvenience of the first of these methods is the requirement for longitudinal mechanical translation of the reference mirror in order to obtain information on the axial structure of the object. This delimits its fast imaging ability and is a source of errors connected with possible non-linearities in mechanical translation.
- a substantial limitation of the second, spectral, method of optical tomography is the speed of data transfer between the linear spectrum detector and the processor performing the numerical Fourier transform. Because the number of detector pixels required for adequate resolution is not less then 1024, parallel connection of every pixel to the processor is currently not practical, necessitating the serial transfer of light intensity data one pixel at a time.
- the purpose of the invention is to provide a method for rapid registration of the whole tomographic image.
- the new method of fast imaging of objects by means of spectral optical coherence tomography using partially coherent light implemented with the light source, an interferometer equipped with a beam splitter and reference mirror, a scanner, a spectrograph, a matrix of sensors, and a data processor, synchronizing the recording of interference spectra with scanning of the probe beam perpendicularly to its direction of propagation, uses one row of the matrix of sensors to record the signals originating from interference spectra for each consecutive point of the object. Simultaneously with movement of the scanner to record the next point in the cross-section of the object, all previously registered spectra are transferred to the memory of the detector matrix. The thus rapidly obtained complete cross-sectional data set in the detector matrix can then be transferred at leisure to the processor and the cross-section image reconstructed by numerical Fourier transform.
- a matrix of detectors as a matrix of detectors is employed a matrix of photo-detectors such that only the terminal row of the photo-detector matrix is used for the registration of the interference spectrum, the other rows being used as memory.
- a matrix of photo-detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of a first scanner which is placed between spectrometer grating and the matrix of detectors, and the other rows of detectors are being used as memory.
- a matrix of photo-detectors is employed as a matrix of detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of an acousto-optical modulator which is placed between spectrometer grating and the matrix of detectors, and the other rows of detectors are being used as memory.
- a matrix of photo-detectors is employed as a matrix of detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of the first actuator changing the orientation of the spectrometer grating, and the other rows of detectors are being used as memory.
- a matrix of photo-detectors comprising internal analogue memory is employed, and the interference spectrum is transferred to this memory in synchronic way to the probing scanner movement.
- a matrix of photo-detectors comprising internal digital memory is employed, and the interference spectrum is transferred to this memory in synchronic way to the probing scanner movement.
- a matrix of photo-detectors is employed as a matrix of detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of the second actuator which is changing the position of the matrix of detectors, and the other rows of detectors are being used as memory.
- a matrix of photo-detectors is employed as a matrix of detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of the second scanner which is placed between interferometer beam- splitter and spectrometer grating, and the other rows of detectors are being used as memory.
- the light beam is irradiating the analyzed object exclusively during registration of the interference spectrum in synchronic way to the probing scanner movements.
- the light beam is controlled by mean of moving disk chopper or tuning fork chopper or by modulation of the light source.
- the essential advantage of the method of present invention is a separation of the process of acquisition and process of processing, enabled by use of memory within the matrix of detectors. Because of this, the whole of the cross-sectional information of the object examined is acquired in a very short time and the object has no time substantially to move. The resultant images are very sharp. Limiting the object irradiation exclusively to the registration time of the interference spectrum, the total energy injected into examined object is favorably reduced, and as a result, a better protection of a patient's eye at the time of retina exposure is obtained.
- the method is presented in detail in implementation examples and illustrated with a diagram, where on Fig. 1, Fig. 2, Fig. 3, Fig. A, Fig. 5 and Fig. 6, embodiments of a set-up that has been used for human retinal examination are provided.
- the set-up consists of a collimator . equipped with a light source 1 comprising super luminescent diode (SLD 381 produced by Superlum, RU) generating a continuous wave beam of light with high spatial coherence but low temporal coherence.
- the beam is rendered quasi-parallel in the collimator • ⁇ and directed to the Michelson interferometer equipped with a beam splitter 2 and reference mirror 3, and to a probing scanner 4 (type 6200, Cambridge Technology, US) equipped with a lens 5.
- Part of the light from the beam splitter 2 is directed through the lens 5 to the object 6 and back to the Michelson interferometer.
- the controller 10 changes the position of the probing beam, and if the camera 9 is set to Bluetooth kinetics" mode, the whole of the information stored in the CCD matrix 8 is advanced by one row. After filling the whole of the CCD matrix 8 with consecutive registered spectra, the whole set of this data is read out into processing computer (not shown in the diagram).
- the optical coherence tomography cross-sectional image of the retina is recovered by Fourier transform analysis of the data by the computer either in real time or after storage in a file.
- Imaging of a cross-section of the retina as object 6 is performed with the patient in front of lens 5 of probing scanner 4 directing the light onto the retinal area to be examined.
- the registration of the interference spectra for the consecutive points of the object is performed under computer control.
- Each of the spectra is registered in the terminal row of the detector matrix 8 and, simultaneously with advancement of the probing scanner 4 to the position of the next point to be investigated, the recorded spectra are advanced by one row until the whole matrix is full.
- the cross-sectional image of the retinal object 6 is recovered from the spectral signals by numerical Fourier transform.
- Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the first scanner 12 which is placed between spectrometer grating 7 and the matrix of detectors 8, and the other rows of detectors are being used as memory.
- a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the first scanner 12 which is placed between spectrometer grating 7 and the matrix of detectors 8, and the other rows of detectors are being used as memory.
- the movements of the first scanner 12 are under control of the controller 10 which operation is synchronized by synchronizator 11.
- Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the acousto-optical modulator 13 which is placed between spectrometer grating 7 and the matrix of detectors 8, and the other rows of detectors are being used as memory.
- a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the acousto-optical modulator 13 which is placed between spectrometer grating 7 and the matrix of detectors 8, and the other rows of detectors are being used as memory.
- the acousto-optical modulator 13 operates under control of the controller 10 which is synchronized by synchronizator ⁇ .
- Example IN
- Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the first actuator 14 changing the orientation of the spectrometer grating 7 , and the other rows of detectors are being used as memory.
- a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the first actuator 14 changing the orientation of the spectrometer grating 7 , and the other rows of detectors are being used as memory.
- the first actuator 14 operates under control of the controller 10 which is synchronized by synchronizator H .
- Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the second actuator 15 changing the position of the matrix of detectors 8 , and the other rows of detectors are being used as memory.
- a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the second actuator 15 changing the position of the matrix of detectors 8 , and the other rows of detectors are being used as memory.
- the second actuator 15 operates under control of the controller 10 which is synchronized by synchronizator H .
- Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the second scanner 16 which is placed between beam-splitter 2 and spectrometer grating 7, and the other rows of detectors are being used as memory.
- a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the second scanner 16 which is placed between beam-splitter 2 and spectrometer grating 7, and the other rows of detectors are being used as memory.
- the movements of the second scanner 16 are under control of the controller 10 which operation is synchronized by synchronizator H.
- the light beam is directed towards the analyzed object 6 exclusively during registration of the interference spectrum by use of rotating disk chopper 17 placed between light source 1 and beam-splitter 2, and synchronized to the movements of probing scanner 4 by the synchronizator H .
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Abstract
The subject of invention is a method of fast imaging of objects by means of spectral optical coherence tomography using partially coherent light comprising a matrix of detectors with a memory, specially suitable for medical imaging. This is accomplished with a partially coherent light source 1, an interferometer equipped with a beam splitter 2 and reference mirror 3, a probing scanner 4, a matrix of sensors with a memory 8, a spectrograph comprising 7, and a data processor. It is distinguished from other methods of synchronization of probing scanner 4 movements with the recording of interference spectra, by recording the signals originating from the interference spectra of consecutive points of the object 6 in the matrix of photo-detectors 8. Simultaneously with the probing scanner 4 movement to the next point in the cross-section of the object 6, all previously registered spectra are transferred to the memory within the detector matrix 8. The information is subsequently transferred to an appropriate data processor and the cross-sectional image reconstructed by means of numerical Fourier transform.
Description
Method of fast imaging of objects by means of spectral optical coherence tomography
The subject of the invention is a method of fast imaging of objects by means of spectral optical coherence tomography using partially coherent light and a matrix of photo-detectors with memory, specially suitable for medical imaging.
One previously known method of imaging of cross-sections of transparent and semi-transparent objects by means of optical coherence tomography using partially coherent light consists in recovering information on the structure of the object along the line of propagation of the penetrating probe beam from the interference signal, and information on consecutive strips in a cross-section of the object by shifting the probe beam perpendicularly to its direction of propagation.
This method is implemented using a Michelson interferometer with a light source of high spatial coherence but low temporal coherence, and by placing the sample to be examined in one arm of the interferometer and the translatable reference mirror in the other arm. The interference signal originating in the interferometer during translation of the reference mirror is registered by a photodiode whose output is filtered with an analog band filter. The signal is then digitized and transferred to a computer. This complete sequence is repeated sequentially for consecutive strips in the cross-section of the image.
The other known method of spectral optical coherence tomography using partially coherent light consists in recording spectral fringes with the spectrograph without translation of the reference mirror. In this method many photo-detectors simultaneously registering the whole spectrum are employed. Information on the axial structure of the object is recovered from the spectral signal by means of numerical Fourier transform.
The inconvenience of the first of these methods is the requirement for longitudinal mechanical translation of the reference mirror in order to obtain information on the axial structure of the object. This delimits its fast imaging ability and is a source of errors connected with possible non-linearities in mechanical translation.
A substantial limitation of the second, spectral, method of optical tomography is the speed of data transfer between the linear spectrum detector and the processor performing the numerical Fourier transform. Because the number of detector pixels required for adequate resolution is not less then 1024, parallel connection of every pixel to the processor is currently not practical, necessitating the serial transfer of light intensity data one pixel at a time.
The purpose of the invention is to provide a method for rapid registration of the whole tomographic image.
It was found that, in the majority of applications of object imaging with spectral optical tomography, especially during the examination of anatomical objects in vivo, it is the time taken to register a given number of consecutive spectra corresponding with consecutive strips in the analyzed tomogram that is important. During this time the object must remain stationary. The time from the end of registration to the end of data processing and visualization of the result is less important, because involuntary object movements during data transfer and mathematical processing are irrelevant.
The new method of fast imaging of objects by means of spectral optical coherence tomography using partially coherent light, implemented with the light source, an interferometer equipped with a beam splitter and reference mirror, a scanner, a spectrograph, a matrix of sensors, and a data processor, synchronizing the recording of interference spectra with scanning of the probe beam perpendicularly to its direction of
propagation, uses one row of the matrix of sensors to record the signals originating from interference spectra for each consecutive point of the object. Simultaneously with movement of the scanner to record the next point in the cross-section of the object, all previously registered spectra are transferred to the memory of the detector matrix. The thus rapidly obtained complete cross-sectional data set in the detector matrix can then be transferred at leisure to the processor and the cross-section image reconstructed by numerical Fourier transform.
In one embodiment of the present invention, as a matrix of detectors is employed a matrix of photo-detectors such that only the terminal row of the photo-detector matrix is used for the registration of the interference spectrum, the other rows being used as memory.
In next embodiment of the present invention as a matrix of detectors a matrix of photo-detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of a first scanner which is placed between spectrometer grating and the matrix of detectors, and the other rows of detectors are being used as memory.
In another embodiment of the present invention as a matrix of detectors a matrix of photo-detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of an acousto-optical modulator which is placed between spectrometer grating and the matrix of detectors, and the other rows of detectors are being used as memory.
In another embodiment of the present invention as a matrix of detectors a matrix of photo-detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of the first actuator changing the orientation of the spectrometer grating, and the other rows of detectors are being used as memory.
In another embodiment of the present invention as a matrix of detectors, a matrix of photo-detectors comprising internal analogue memory is employed, and the interference spectrum is transferred to this memory in synchronic way to the probing scanner movement.
In another embodiment of the present invention as a matrix of detectors, a matrix of photo-detectors comprising internal digital memory is employed, and the interference spectrum is transferred to this memory in synchronic way to the probing scanner movement.
In another embodiment of the present invention as a matrix of detectors a matrix of photo-detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of the second actuator which is changing the position of the matrix of detectors, and the other rows of detectors are being used as memory.
In another embodiment of the present invention as a matrix of detectors a matrix of photo-detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the probing scanner movement by means of the second scanner which is placed between interferometer beam- splitter and spectrometer grating, and the other rows of detectors are being used as memory.
In embodiments of the present invention, the light beam is irradiating the analyzed object exclusively during registration of the interference spectrum in synchronic way to the probing scanner movements. The light beam is controlled by mean of moving disk chopper or tuning fork chopper or by modulation of the light source.
The essential advantage of the method of present invention is a separation of the process of acquisition and process of processing, enabled by use of memory within the matrix of detectors. Because of this, the whole of the cross-sectional information of the object examined is acquired in a very short time and the object has no time substantially to move. The resultant images are very sharp. Limiting the object irradiation exclusively to the registration time of the interference spectrum, the total energy injected into examined object is favorably reduced, and as a result, a better protection of a patient's eye at the time of retina exposure is obtained.
The method is presented in detail in implementation examples and illustrated with a diagram, where on Fig. 1, Fig. 2, Fig. 3, Fig. A, Fig. 5 and Fig. 6, embodiments of a set-up that has been used for human retinal examination are provided.
E x a m p l e I:
As illustrated in the diagram Fig.l, the set-up consists of a collimator . equipped with a light source 1 comprising super luminescent diode (SLD 381 produced by Superlum, RU) generating a continuous wave beam of light with high spatial coherence but low temporal coherence. The beam is rendered quasi-parallel in the collimator •< and directed to the Michelson interferometer equipped with a beam splitter 2 and reference mirror 3, and to a probing scanner 4 (type 6200, Cambridge Technology, US) equipped with a lens 5. Part of the light from the beam splitter 2 is directed through the lens 5 to the object 6 and back to the Michelson interferometer. Light scattered off the object 6 and light reflected from the reference mirror 3 is simultaneously dispersed by the diffraction grating (1800 grooves/mm, Spectragon AB, S) of a spectrograph 7 and the interference spectrum is recorded in the terminal upper row of the matrix of sensors 8 of the CCD camera 9 (type DN401, Andor Technology, GB). Scanner motions are controlled by module 10. The camera 9 and the controlling module JLO are set in register by directing an electronic triggering pulse from a synchronizer module 11 simultaneously to the controlling module 10 and to the ,-EXT. TRIG." input of the camera 9. In response to this pulse, the controller 10 changes the position of the probing beam, and if the camera 9 is set to „fast kinetics" mode, the whole of the information stored in the CCD matrix 8 is advanced by one row. After filling the whole of the CCD matrix 8 with consecutive registered spectra, the whole set of this data is read out into processing computer (not shown in the diagram). The optical coherence tomography cross-sectional image of the retina is recovered by Fourier transform analysis of the data by the computer either in real time or after storage in a file.
Imaging of a cross-section of the retina as object 6 is performed with the patient in front of lens 5 of probing scanner 4 directing the light onto the retinal area to be examined.
The registration of the interference spectra for the consecutive points of the object is performed under computer control. Each of the spectra is registered in the terminal row of the detector matrix 8 and, simultaneously with advancement of the probing scanner 4 to the position of the next point to be investigated, the recorded spectra are advanced by one row until the whole matrix is full. The cross-sectional image of the retinal object 6 is recovered from the spectral signals by numerical Fourier transform.
Example II.
The method of invention is illustrated by Fig. 2. Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the first scanner 12 which is placed between spectrometer grating 7 and the matrix of detectors 8, and the other rows of detectors are being used as memory.
The movements of the first scanner 12 are under control of the controller 10 which operation is synchronized by synchronizator 11.
Example m
The method of invention is illustrated by Fig. 3. Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the acousto-optical modulator 13 which is placed between spectrometer grating 7 and the matrix of detectors 8, and the other rows of detectors are being used as memory.
The acousto-optical modulator 13 operates under control of the controller 10 which is synchronized by synchronizator ϋ .
Example IN
The method of invention is illustrated by Fig. 4. Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the first actuator 14 changing the orientation of the spectrometer grating 7 , and the other rows of detectors are being used as memory.
The first actuator 14 operates under control of the controller 10 which is synchronized by synchronizator H .
Example V
The method of invention is illustrated by Fig. 5. Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the second actuator 15 changing the position of the matrix of detectors 8 , and the other rows of detectors are being used as memory.
The second actuator 15 operates under control of the controller 10 which is synchronized by synchronizator H .
Example NI
The method of invention is illustrated by Fig. 6. Imaging of the object 6 is performed as in the Example I, wherein as a matrix of detectors 8 a matrix of photo- detectors is employed, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner 4 by means of the second scanner 16 which is placed between beam-splitter 2 and spectrometer grating 7, and the other rows of detectors are being used as memory.
The movements of the second scanner 16 are under control of the controller 10 which operation is synchronized by synchronizator H.
The light beam is directed towards the analyzed object 6 exclusively during registration of the interference spectrum by use of rotating disk chopper 17 placed between light source 1 and beam-splitter 2, and synchronized to the movements of probing scanner 4 by the synchronizator H .
Claims
1. A method of fast imaging of objects by means of spectral optical coherence tomography using partially coherent light implemented with a light source, an interferometer equipped with a beam splitter and reference mirror, a scanner, a matrix of sensors, a spectrograph and a data processor, characterized in that the recording of interference spectra originating from consecutive points of the object 161 is synchronic with movement of the probing scanner lAl in such way that each spectrum obtained is registered in a row of the detector matrix /§/, all previously registered spectra being transferrd to the memory of the matrix of detectors /8/ simultaneously with the advance of the probing scanner IAJ to the next point in the cross-section of the object 161, and the information later being transferred to an appropriate data processor in which cross-sectional image is reconstructed by means of numerical Fourier transform.
2. The method of claim 1 characterized in that as a matrix of detectors /8/ is used a matrix of photo-detectors such that only the terminal row of the photo-detector matrix is used for the registration of the interference spectrum, the other rows being used as memory.
3. The method of claim 1 characterized in that as a matrix of detectors /8/ is used a matrix of photo-detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner /4/ by means of the first scanner 712/ which is placed between spectrometer grating 111 and the matrix of detectors /8/, and the other rows of detectors are being used as memory.
4. The method of claim 1 characterized in that as a matrix of detectors /§/ is used a matrix of photo-detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner /4/_ by means of the acousto-optical modulator 713/ which is placed between spectrometer grating 111 and the matrix of detectors /8 , and the other rows of detectors are being used as memory.
5. The method of claim 1 characterized in that as a matrix of detectors /8/ is used a matrix of photo-detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner I t by means of the first actuator 714/ changing the orientation of the spectrometer grating III , and the other rows of detectors are being used as memory.
6. The method of claim 1 characterized in that as a matrix of detectors /§/ is used a matrix of photo-detectors comprising internal analogue memory.
7. The method of claim 1 characterized in that as a matrix of detectors /8/_ is used a matrix of photo-detectors comprising internal digital memory.
8. The method of claim 1 characterized in that as a matrix of detectors /8/_ is used a matrix of photo-detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner /4/_ by means of the second actuator 715/ changing the position of the matrix of detectors /8/_ , and the other rows of detectors are being used as memory.
9. The method of claim 1 characterized in that as a matrix of detectors /8/_ is used a matrix of photo-detectors, and the interference spectrum is directed towards a new row of detectors in synchronic way to the movement of probing scanner /4/ by means of the second scanner 716/ which is placed between beam-splitter I2 and spectrometer grating 111, and the other rows of detectors are being used as memory.
10. The method of claim 1 or 2 or 3 or 4 or 5 or 6 or 7 or 8 or 9, characterized in that the light beam is irradiating the analyzed object 161 exclusively during registration of the interference spectrum in synchronism with movements of probing scanner I J.
11. The method of claim 10 characterized in that the light beam is obturated by chopper /17/ comprising rotating perforated disk.
12. The method of claim 10 characterized in that the light beam is obturated by chopper 717/ comprising tuning fork.
13. The method of claim 10 characterized in that the light beam is switched on and off by mean of modulation of the light source /!/.
Applications Claiming Priority (6)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| PL357000A PL205340B1 (en) | 2002-11-07 | 2002-11-07 | Method of fast object imaging by means of spectral optical tomography in partially coherent light |
| PLP-357000 | 2002-11-12 | ||
| PLP-362154 | 2003-08-12 | ||
| PL362154A PL206508B1 (en) | 2003-09-12 | 2003-09-12 | Light beam intensity control system for optical spectral tomography apparatus |
| PLP-363410 | 2003-11-12 | ||
| PL363410A PL206507B1 (en) | 2003-11-12 | 2003-11-12 | Method for quick object imaging using spectral optical tomography in partially coherent light |
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| WO2004043245A1 true WO2004043245A1 (en) | 2004-05-27 |
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| PCT/PL2003/000118 WO2004043245A1 (en) | 2002-11-07 | 2003-11-12 | A method of fast imaging of objects by means of spectral optical coherence tomography |
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Cited By (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP1602320A1 (en) * | 2004-06-03 | 2005-12-07 | Nidek Co., Ltd. | Ophtalmic apparatus |
| WO2006020605A2 (en) * | 2004-08-10 | 2006-02-23 | The Regents Of The University Of California | Device and method for the delivery and/or elimination of compounds in tissue |
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| WO2006058735A1 (en) * | 2004-12-02 | 2006-06-08 | Carl Zeiss Meditec Ag | Enhanced optical coherence tomography for anatomical mapping |
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| EP1870028A1 (en) | 2006-06-23 | 2007-12-26 | OPTOPOL Technology Spolka z o.o. | Apparatus and method for frequency domain optical coherence tomography |
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| EP2000081A1 (en) | 2007-06-07 | 2008-12-10 | OPTOPOL Technology Spolka Akcyjna | Apparatus for optical frequency domain tomography with adjusting system |
| DE102007046504A1 (en) | 2007-09-28 | 2009-04-02 | Carl Zeiss Meditec Ag | spectrometer |
| US7982881B2 (en) | 2005-12-06 | 2011-07-19 | Carl Zeiss Meditec Ag | Apparatus and method for interferometric measurement of a sample |
| US8049899B2 (en) | 2005-11-10 | 2011-11-01 | Haag-Streit Ag | Method and apparatus for determination of geometric values on a transparent or diffusive object |
| RU2459197C1 (en) * | 2008-07-07 | 2012-08-20 | Кэнон Кабусики Кайся | Imaging apparatus and imaging method using optical coherence tomography |
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| US8764189B2 (en) | 2006-03-16 | 2014-07-01 | Carl Zeiss Meditec, Inc. | Methods for mapping tissue with optical coherence tomography data |
| US8913793B2 (en) | 2005-09-09 | 2014-12-16 | Carl Zeiss Meditec, Inc. | Method of bioimage data processing for revealing more meaningful anatomic features of diseased tissues |
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| US9791684B2 (en) | 2010-01-06 | 2017-10-17 | Ecole polytechnique fédérale de Lausanne (EPFL) | Optical coherence microscopy system having a filter for suppressing a specular light contribution |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE4309056A1 (en) * | 1993-03-20 | 1994-09-22 | Haeusler Gerd | Method for determining the distance and intensity of scattering of the scattering points |
| US5565986A (en) * | 1994-03-30 | 1996-10-15 | Kn+E,Uml U+Ee Ttel; Alexander | Stationary optical spectroscopic imaging in turbid objects by special light focusing and signal detection of light with various optical wavelengths |
| US6377349B1 (en) * | 1998-03-30 | 2002-04-23 | Carl Zeiss Jena Gmbh | Arrangement for spectral interferometric optical tomography and surface profile measurement |
-
2003
- 2003-11-12 WO PCT/PL2003/000118 patent/WO2004043245A1/en active Search and Examination
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE4309056A1 (en) * | 1993-03-20 | 1994-09-22 | Haeusler Gerd | Method for determining the distance and intensity of scattering of the scattering points |
| US5565986A (en) * | 1994-03-30 | 1996-10-15 | Kn+E,Uml U+Ee Ttel; Alexander | Stationary optical spectroscopic imaging in turbid objects by special light focusing and signal detection of light with various optical wavelengths |
| US6377349B1 (en) * | 1998-03-30 | 2002-04-23 | Carl Zeiss Jena Gmbh | Arrangement for spectral interferometric optical tomography and surface profile measurement |
Non-Patent Citations (3)
| Title |
|---|
| LEITGEB R ET AL: "SPECTRAL MEASUREMENT OF ABSORPTION BY SPECTROSCOPIC FREQUENCY-DOMAIN OPTICAL COHERENCE TOMOGRAPHY", OPTICS LETTERS, OPTICAL SOCIETY OF AMERICA, WASHINGTON, US, vol. 25, no. 11, 20 June 2000 (2000-06-20), pages 820 - 822, XP000951878, ISSN: 0146-9592 * |
| WOJTKOWSKI MACIEJ ET AL: "In vivo human retinal imaging by Fourier domain optical coherence tomography.", JOURNAL OF BIOMEDICAL OPTICS. UNITED STATES JUL 2002, vol. 7, no. 3, July 2002 (2002-07-01), pages 457 - 463, XP002272406, ISSN: 1083-3668 * |
| WOJTKOWSKI MACIEJ ET AL: "Real-time in vivo imaging by high-speed spectral optical coherence tomography.", OPTICS LETTERS. UNITED STATES 1 OCT 2003, vol. 28, no. 19, 1 October 2003 (2003-10-01), pages 1745 - 1747, XP002272407, ISSN: 0146-9592 * |
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