• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    SCAN DEVICE FOR LOW COHERENCE INTERFEROMETRY. A system for lateral scanning of a sample using optical coherence tomography is presented. The low coherence interferometry system includes a first multiplexing unit and a second multiplexing unit. The first multiplexing unit is configured to receive a first beam of radiation, and includes a first plurality of optical delay elements configured to introduce a group delay for the first beam of radiation based on an optical path traveled by the first beam of radiation between a first plurality of optical waveguides. The second multiplexing unit is configured to receive a second beam of radiation. The second multiplexing unit includes a second plurality of optical modulation elements configured to differentiate the second radiation beam between a second plurality of optical waveguides for the production of one or more outgoing radiation beams. The second plurality of optical waveguides is configured to orient one or more beams of output radiation towards a sample.
    公开号:BR112013029785B1
    申请号:R112013029785-9
    申请日:2012-05-18
    公开日:2021-01-05
    发明作者:José Luis Rubio Guivernau；Eduardo MARGALLO BALBÁS
    申请人:Medlumics, S.L.；
    IPC主号:
    专利说明:

    FIELD
    [0001] Modalities of the invention refer to high resolution optical coherence tomography fields. FUNDAMENTALS
    [0002] Optical Coherence Tomography (OCT) is a technique for generating medical images that can provide axial information in high resolution using a broadband light source and an interferometry detection system. A wide variety of uses have been found, from cardiology to ophthalmology and gynecology, or for in vitro sectional studies of biological materials.
    [0003] Axial information is obtained in OCT by means of interferometry methods. To generate images (2D) and volume representations (3D) of tissue histology, it is necessary to move the bundle laterally along the area of interest. This movement has traditionally been done by means of mechanical displacement of some optical element inside the system, such as the waveguide in the case of fiber based systems. Alternatively, the sample can be moved under a stationary beam. The most common solution uses a moving mirror in the beam path on the sample arm of the interferometer. Although this method is effective, it has disadvantages, especially in terms of reliability, manufacturing cost, maintenance costs, adjustment complexity, final system size, etc. The use of MOEMS technology (micro-opto-electromechanical systems) has been proposed and demonstrated for situations in which conventional mirrors are not acceptable, such as catheters or laparoscopic instruments. However, these devices suffer from many of the same problems as their macroscopic versions and they pose their own challenges in terms of encapsulation, sterilization, etc.
    [0004] One approach for providing a side scan over a sample is to use multiple beams. An example of this was proposed in patent application WO 2010/134624. Several complete interferometers that work in parallel are described that only share the light source. As such, the sample arm of each interferometer consists of a single optical path and there is no multiplexing mechanism that leads to a structurally complicated system.
    [0005] Another patent application, document WO 2004/073501, contemplates the use of multiple bundles that are simultaneously incident on the sample. The purpose of this patent application is to combine these beams in a controlled manner through the use of modulators and phase delays. The combined lighting over the sample shows a certain pattern of interference. Working with the modulators and phase delay elements, the position of the light interference pattern in the sample can be varied and, subsequently, it is possible to reconstruct a three-dimensional image of the sample using signal processing techniques. The application does not use multiplexing means to distinguish light collected from a plurality of optical paths. There is only a single optical path that collects the reflected light from the sample.
    [0006] In an article by Yamanari et. Al, "Scanned source optical coherence tomography sensitive to full-range polarization by simultaneous transversal and spectral modulation", Optics Express Vol. 18, Edition 13, pp 13.964-13.980 of 2010, a polarization sensitive SS-OCT system (OCT Source) is described. In this system, and in order to solve the problem of typical complex complexes of SS-OCT and FD-OCT (Fourier Domain OCT) systems, phase modulation is applied to the reference arm. This phase is modified while electromechanical means scan the sample laterally. This document, therefore, does not describe the use of modulation in the sample arm. In addition, in the case of time domain OCT (TD-OCT) systems, the sweep speed of the variable delay element in the reference arm may be a limitation on the performance of the final system, insofar as its operating speed or Maximum scan range may be insufficient for the application of interest. U.S. Patent 6198540 and EP Patent Application 1,780,530 each describe systems that use multiple optical paths in the reference arm. However, each system uses traditionally free optical spaces and mechanical means for lateral scanning of the sample. BRIEF SUMMARY
    [0007] The systems and methods for conducting a low coherence side scan of a sample while minimizing (and in some modalities eliminating) the use of mechanical elements are presented. In one embodiment, the system divides a sample arm into several optical paths and uses a plurality of outputs that send and receive beams to and from different areas of a sample, thus maintaining the ability to differentiate the light received at any time. from reflections at different depths within the sample.
    [0008] According to one embodiment, a low coherence interferometry system includes a first multiplexing unit and a second multiplexing unit. The first multiplexing unit is configured to receive a first beam of radiation, and includes a first plurality of optical delay elements. The first plurality of optical delay elements is configured to introduce a group delay for the first radiation beam based on an optical path traveled by the first radiation beam between a first plurality of optical waveguides. The second multiplexing unit is configured to receive a second beam of radiation. In one embodiment, the second beam of radiation is the same as the first beam of radiation. In another embodiment, the second beam of radiation is different from the first beam of radiation. The second multiplexing unit includes a second plurality of optical modulation elements. The second plurality of optical modulation elements is configured to differentiate the second radiation beam between a second plurality of optical waveguides to produce one or more outgoing radiation beams. The second plurality of optical waveguides is configured to orient one or more beams of output radiation towards a sample.
    [0009] In one embodiment, a method includes receiving a beam of radiation in a first multiplexing unit. Then, a group delay is introduced for the radiation beam received in the first multiplexing unit based on an optical path taken by the radiation beam received in the first multiplexing unit between a first plurality of optical waveguides in the first unit of multiplexing. A beam of radiation is received in a second multiplexing unit. In one embodiment, the radiation beam received in the second multiplexing unit is the same as the radiation beam received in the first multiplexing unit. In another embodiment, the radiation beam received in the second multiplexing unit is different from the radiation beam received in the first multiplexing unit. The radiation beam received in the second multiplexing unit is differentiated in the second multiplexing unit between a second plurality of optical waveguides for the production of one or more output radiation beams. The one or more output radiation beams are oriented towards a sample. BRIEF DESCRIPTION OF THE DRAWINGS / FIGURES
    [0010] The accompanying drawings, which are incorporated here and constitute a part of the specification, illustrate modalities of the present invention and, together with the description, serve, in addition, to explain the principles of the invention and to allow an expert in the relevant art make and use the invention.
    [0011] Figure 1 illustrates a block diagram of an OCT system according to a modality.
    [0012] Figure 2 illustrates a block diagram of a lateral scanning system, according to one modality.
    [0013] Figure 3 illustrates an example of a time division multiplexing unit.
    [0014] Figures 4-6 illustrate examples of first multiplexing units, according to modalities.
    [0015] Figures 7-12 illustrate examples of second multiplexing units, according to the modalities.
    [0016] Figure 13 illustrates the use of beam targeting elements with the second multiplexing unit, according to one modality.
    [0017] Figures 14-15 illustrate examples of the use of one or more optical elements to focus the light, according to the modalities.
    [0018] Figure 16 illustrates a sample depth scanning technique according to a modality.
    [0019] Figure 17 illustrates the use of a gradient index lens with the multiplexing units, according to one modality.
    [0020] Figures 18A-B illustrate two views of an optical reflection element with the multiplexing units, according to one modality.
    [0021] Figures 1-20 illustrate the use of adjustable reflection elements with the multiplexing units, according to modalities.
    [0022] Figure 21 illustrates a flow chart of an example method, according to a modality.
    [0023] Modalities of the present invention will be described with reference to the accompanying drawings. DETAILED DESCRIPTION
    [0024] Although specific configurations and provisions are discussed, it should be understood that this is done for illustrative purposes only. One skilled in the pertinent art will recognize that other configurations and arrangements can be used without departing from the spirit and scope of the present invention. It will be apparent to one skilled in the pertinent art that this invention can also be used in a variety of other applications.
    [0025] Note that references in the specification for "a modality," "a modality," "an example modality," etc., indicate that the described modality may include a particular feature, structure, or feature, but each modality may not necessarily include the particular feature, structure, or feature. Furthermore, these phrases do not necessarily refer to the same modality. Furthermore, when a particular feature, structure, or feature is described in connection with a modality, it would be within the knowledge of a person skilled in the art to effect such a feature, structure or feature in connection with other modalities whether or not explicitly described.
    [0026] Modalities described here provide for sample scanning using optical coherence tomography (OCT) while avoiding or minimizing the use of moving mechanical parts for the lateral displacement of the beam through the sample. In addition, modalities provide certain advantages such as an increase in the effectiveness of axial scanning. Spatial diversity schemes can be implemented by measuring the same sample region from different directions simultaneously, which reduces smearing and other types of noise in measurements. In addition, measurements of sample light scattering in different directions can be collected, thus providing information on sample dispersion anisotropy and directionality.
    [0027] In various modalities, different optical paths for a radiation beam to travel are distinguished only by means of multiplexing techniques that allow the separation of different spatial positions during image processing. Any multiplexing technique can be applicable (time domain, frequency, code division, etc.). In one example, time domain multiplexing can be advantageously combined with other multiplexing techniques, such as frequency multiplexing. Discussed below is an example of the OCT system that includes multiplexing capabilities to produce multiple output paths for the radiation beam to travel.
    [0028] Figure 1 illustrates an OCT 101 system, using an optical compensation element 112, and used to image a sample 110, according to an embodiment. For example, optical compensation element 112 can compensate for chromatic dispersion or any other type of light aberration within the OCT 101 system. In another example, compensation element 112 can only reflect back incoming light without applying any particular modulation to the light . The use of the term "light" can refer to any range of the electromagnetic spectrum. In one embodiment, the term "light" refers to infrared radiation at a wavelength of about 1.3 μm. OCT system 101 further includes an optical source 102, a dividing element 104, a sample arm 106, a reference arm 108, a detector 114, and a scanning system 116. In the embodiment shown, compensation element 112 is located within of reference arm 108, however, it should be understood that compensation element 112 can also be located on sample arm 106. Alternatively, compensation element 112 can be present on both sample arm 106 and reference arm 108. In one For example, sample arm 106 and reference arm 108 are optical waveguides like standard waveguides or optical fibers. In one embodiment, all components of the OCT 101 system are integrated into a flat light wave (PLC) circuit. Other implementations can also be considered, such as, for example, optical fiber systems, free space optical systems, photonic crystal systems, etc.
    [0029] It should be understood that OCT 101 system can include any number of other optical elements not shown for the sake of clarity. For example, OCT 101 system may include mirrors, lenses, grids, dividers, micromechanical elements, etc., along the sample arm 106 or reference arm paths 108. OCT 101 system can include several modulation elements configured to suppress contributions interference signals generated in non-active optical paths. In another example, the OCT 101 system may include MEMS (Micro Electro Mechanical Systems), which apply an additional physical side scan to the beams. An optical element in the light path can be moved through electromechanical actuators (for example, based on thermal expansion, electrostatic or piezoelectric force) that are integrated using microfabrication techniques.
    [0030] Split element 104 is used to direct light received from the optical source 102 to both sample arms 106 and reference arm 108. Split element 104 can be, for example, a bidirectional coupler, an optical divider, or any other optical modulation device that converts a single beam of light into two or more beams of light.
    [0031] Light that travels through sample arm 106 passes through scanning system 116 before finally colliding with sample 110. Scanning system 116 can include one or more multiplexing units, with each unit differentiating light between a plurality of optical paths . For example, scanning system 116 may include a multiplexing unit that selects an optical path associated with a given group delay. The group delay applied to the light as it travels the selected path determines a scanning depth of the light in the sample 110. In another example, scanning system 116 may include another multiplexing unit that differentiates the light between a plurality of output wave to produce one or more output radiation beams. The outgoing radiation beams can collide with sample 110 in different regions in sample 110 and can be directed from different directions. More details on the different multiplexing units are discussed here.
    [0032] Sample 110 can be any sample suitable for imaging, such as tissue. During an OCT procedure, light sweeps to a certain depth inside sample 110 and scattered radiation is collected back to sample arm 106. In another embodiment, scattered radiation is collected back to a different waveguide from the transmission waveguide.
    [0033] Light inside sample arm 106 and reference arm 108 is recombined before being received at detector 114. In the mode shown, the light is recombined by division element 104. In another embodiment, the light is recombined in one optical coupling element different than division element 104.
    [0034] In one embodiment, using scanning system 116 for different scanning depths increases the performance of the rest of the OCT 101 system. Due to the different group delays applied to light in scanning system 116, detected interference signals can be separated ( time, frequency, space, code, etc.) for each scanning depth in detector 114. OCT 101 system can be used with all types of scanning systems, including time domain, frequency domain and scanned source.
    [0035] In another embodiment, a subset of the outgoing radiation beams is directed to the same sample area 110, so that measurements for this area are obtained from different directions. In this way, angular diversity can be used to reduce noise in measurements, as described in "Matrix detection for spot reduction in optical coherence microscopy," JM Schmitt, Phys. Med. Biol. vol. 42, issue 7, 1997, the disclosure of which has been incorporated by reference in its entirety. Since the total distance traveled by each radiation beam in the subset will be different, the scanning depth can be controlled independently for each optical path.
    [0036] In another embodiment, an angular light scattering function from sample 110 can be measured from directions other than the incident direction, to provide valuable information about sample anisotropy. Such measurements are possible due to the plurality of output waveguides in the scanning system 116 that can be configured to face the same region of the sample 110. In addition, the scanning depth can be independently controlled for each optical path to take into account any differences in light path distance.
    [0037] Figure 2 illustrates a first multiplexing unit 17 and a second multiplexing unit 9, according to an embodiment. Each multiplexing unit can be a part of the scanning system 116 illustrated in Figure 1. First multiplexing unit 17 receives a beam of radiation from a waveguide 7. First multiplexing unit 17 applies a group delay to the beam of radiation based on an optical path selected within the first multiplexing unit 17. In one example, the optical path is chosen based on time division multiplexing. In another example, light is differentiated between a plurality of optical paths based on frequency division multiplexing. "Differentiation," as used here, may refer to directing light down one or more specific optical paths (as may be the case with time division multiplexing, for example). "Differentiation," as used herein, can also refer to causing light to pass through a certain optical path to be distinguished from light through other optical paths, even if light is crossing these optical paths at the same time (as may be the case with division multiplexing) coherence or frequency division multiplexing, for example). More detailed examples of the first multiplexing unit 17 are illustrated in Figures 4-7.
    [0038] Second multiplexing unit 9 receives the radiation beam from the first multiplexing unit 17. Although only a single waveguide is illustrated connecting the two multiplexing units, it should be understood that any number of waveguides can be used to transfer light between the two multiplexing units. Second multiplexing unit 9 differentiates the received beam of radiation between a plurality of outgoing waveguides 8 to produce one or more outgoing radiation beams. In one example, this differentiation is accomplished through time division multiplexing. In another example, differentiation is done through frequency division multiplexing. In another example, differentiation is carried out through multiplexing by coherence domain. It should be understood that any combination of the techniques mentioned above can also be used to differentiate the radiation beam between the output waveguides 8. More detailed examples of the second multiplexing unit 9 are illustrated in Figures 8-14.
    [0039] Several modalities describe at least one form of multiplexing between an input waveguide and one or more output waveguides to separate the different spatial positions in an image processing time. Any type of multiplexing (time division, frequency, coherence, code division, etc.) is applicable. Although embodiments here may illustrate first multiplexing unit 17 and second multiplexing unit 9 being a part of sample arm 106, it should be understood that this does not have to be the case. For example, in any of the previous embodiments, the first multiplexing unit 17 can be located on the reference arm 108 while the second multiplexing unit 9 is located on the sample arm 106. In this example, the first multiplexing unit modulates light on the reference arm 108 , while the second multiplexing unit modulates light in the sample arm 106.
    [0040] Figure 3 illustrates an example of light multiplexing for a relatively small number of outputs, but it can be considered analogous for a larger number as well. Each optical switch 2 diverts light from an incoming waveguide to one of two output waveguides. Switch 2 can be implemented using integrated optical elements, such as Mach-Zehnder interferometers or 2x2 configurable couplers. In addition, modulation elements such as electro-optical, thermo-optical and acoustic-optical modulators can be implemented to direct light between the various waveguides. In one embodiment, optical switches 2 are sufficiently broadband to run efficiently across the entire light spectrum used in the OCT 101 system. Figure 3 also illustrates one of the possible selectable optical paths 10 through the use of switches 2.
    [0041] According to one modality, scanning system 116 includes a multiplexing system for different depth scanning ranges. One of the objectives is to reduce the demands on the axial scan speed or its maximum range, or to increase the actual scan speed given some features of the element in the reference arm 108 of the OCT 101 system. High lateral scan speeds can be achieved using the multiplexing features illustrated in Figure 3.
    [0042] Figures 4A and 4B illustrate two examples of the first multiplexing unit 17, labeled 401 and 402, in the frequency domain for different depth scan ranges by inserting delay elements 11. Delay elements 11 cause delays of group defined in the light that passes through them in the different optical paths 10. Multiplexing units 401 and 402 also include modulation elements 3 used to differentiate the light, for example, in the frequency domain, between the various optical paths through delay elements 11.
    [0043] The positioning of delay elements 11 in the multiplexing unit 401 each adds a delay to its respective portion of the optical path. An optical path having a desired delay, such as optical path 10, can then be selected by adding appropriate delays together along the optical path. The positioning of the modulating elements 3 in the multiplexing unit 402 modulates a relative decrease in added delay in each optical path 10. The objective is to produce a plurality of possible optical paths 10, each with a different total group delay. In this way, a desired group delay can be implemented in the OCT system to image different depths without moving parts. In one example, each of these optical paths 10 is modulated using a characteristic frequency. Delay elements 11 can be implemented in a variety of ways, such as using waveguide segments of different lengths or waveguide segments allowing modification of the refractive index through some effects such as thermo-optical, thermoelectric, load injection, etc. Frequency modulation can be achieved by using modulation elements 3 with a linear behavior in the range [0.2n], as it appears in the interference signal that is collected in the detector 114.
    [0044] Figures 4A-4B show designs based on a sequence of cascade couplers 5, as 2x2 couplers, which are characterized by their conservative nature in terms of optical energy. In fact, all of the optical power is transmitted to the branch waveguides in each cascade coupler 5 between elements. Despite the similarity of the design to a cascaded Mach-Zehnder interferometer, there are no interference effects that occur in the elements, as all relative introduced delays are much greater than the coherence length of the source.
    [0045] In any 401 or 402 multiplexing unit, for different sweep depth ranges shown in Figures 4A-4B, the goal is not to find a complete depth-to-frequency transformation, but a multiplexing of depth ranges through division frequency. The complete transformation can cause some of the relative delays to be comparable to, or less than, the coherence length of the source, in the event that interference effects would appear. The division into the various possible optical paths 10 with different accumulated group delays can also be achieved using, for example, time division multiplexing.
    [0046] Figure 5 illustrates another example of the first multiplexing unit 17 (labeled 501) that includes optical switching elements 2 in a first network 502 and a second network 504. Multiplexing unit 501 further includes delay elements 11. In In one embodiment, delay elements 11 are configured to apply different group delays depending on the selected optical path 10. In one example, second network 504 of optical switches 2 guides light from any of the plurality of possible optical paths through delay elements 11 to a single waveguide output. Since optical switches 02 may not be ideal, some light may leak into paths other than the intended optical path 10. The noise produced by this leaked light can cause problems with the wide dynamic range characteristics of heterodyne detection systems commonly used in OCT. In one embodiment, to mitigate the situation in relation to the light emitted, optical modulators 3 can be inserted in each optical path, in such a way that they are capable of modulating light individually in a given path. In one example, modulation is performed using phase modulators. Thus, the light in the optical path 10 is shifted in frequency with respect to the other optical paths, suppressing possible interference. It should be understood that if optical switches 2 have a sufficiently high switching ratio, then optical modulators 3 may not be necessary.
    [0047] The configuration shown in the multiplexing unit 501 allows individual selection of group delays for each optical path 10, which can be useful to define different scan areas. In another mode, uniform spacing can be achieved across the entire scan range using a simpler design.
    [0048] For example, another example of the first multiplexing unit 17 is illustrated in Figures 6A-B (labeled 601). Multiplexing unit 601 is able to select an optical path 10 with a single group delay, but with a smaller number of delay elements 11 and optical switches 2 than the modality shown in Figure 5. In one embodiment, optical modulators 3 can included in each switchable optical path 10, as shown in Figure 6A. In this way, the selected optical path 10 is modulated, for example, at a single frequency, so that the light can be filtered from other optical paths. Similar to the above discussion with respect to Figure 5, if switching technology is able to minimize light that leaks into an unwanted path, or if interference is discarded from the signals through other means, then optical modulators 3 can be removed . An example multiplexing configuration without optical modulators 3 is illustrated in Figure 6B.
    [0049] Time multiplexing systems have a possible advantage in terms of optical power efficiency. Although the use of the first multiplexing system 17 for different depth scan ranges, such as the examples illustrated in Figures 4 and 6, is relatively efficient in terms of conserving optical power, half of the optical power is lost at its output once that there are two outgoing waveguides. In one embodiment, a form of phase modulation is applied to the two output branches to allow their separation in the frequency domain. In addition, a second multiplexing unit 9 can be included to receive output from both branches. Time division multiplexing systems offer an advantage, that is, the flexibility to select a particular scan region. For example, it is possible to obtain an image with interwoven depth ranges, giving higher priority to certain depth ranges of the image, which would be scanned more often than others, or even concentrate scanning time on a subset of all available ranges. during operation.
    [0050] In one embodiment, optical switches 2 can be designed to switch between a balanced directional optical coupler and an appropriate switch. Thus, advantages of multiplexing in the frequency domain and the time domain could be combined. For example, optical switches 2 can be left in a balanced directional optical coupler state to make multiple depth bands illuminated simultaneously, while other switches can be switched conventionally for sequential access to a particular optical path.
    [0051] If optical detectors 2 acting as couplers allow the distribution of energy between their branches in a controlled and flexible manner (for example, with a variable division ratio), then it is possible to divide the value of the optical power used to sample in each depth. The power can be adjusted to obtain a uniform signal-to-noise ratio, or in another optimal way for the specific application. Alternatively, this can be achieved in the time domain by adjusting the depth scan duration for each first multiplexing unit configuration 17, or accumulating a variable number of lines depending on the depth. The various time multiplexing modalities can result in different periods of time being assigned to configurations of optical switches 2 belonging to different optical paths 10.
    [0052] In one embodiment, multiplexing is introduced in some way for the separate contributions of both output branches of the first multiplexing unit 17. For example, frequency modulation, time multiplexing, or introducing a differential delay in one of the branches that are larger than the scan range are all multiplexing projects that can be implemented. In the last example, it may be necessary that there are no signals with significant magnitude coming from tissue depths greater than the scanning distance, in order to avoid interference between the branches.
    [0053] Figure 7 illustrates an example of a second multiplexing unit 9 (labeled 701) using time division multiplexing, according to a modality. The illustrated system includes waveguide 7, output waveguides 8, first multiplexing unit 17 and multiplexing unit 701. Figure 7 illustrates a possible combination of any sweep range multiplexing system with a time multiplexing system for lines in the lateral direction. This maximizes the use of the available light power and signal-to-noise ratio of the device. In this system, a desired optical path 10 can be selected using optical switches 2 to direct light to a particular waveguide 8. Paths can be selected sequentially, for example, to achieve a scanning functionality where light is passed through each guide wave 8 in a sequential manner.
    [0054] Figure 8 illustrates an example in which the time division multiplexing of the second multiplexing unit 9 has been replaced by a frequency multiplexing unit 801. Frequency multiplexing unit 801 includes optical paths 10 associated with the different lines side scanners, according to a modality. Each branch of the optical path 10 can have an associated optical modulator 3. In one example, a tree of directional couplers is used to divide the received light between all the optical paths. Frequency multiplexing unit 801 has an added advantage of allowing simultaneous detection of all existing scan lines. However, there is a loss of light energy collected by each output waveguide 8 when traveling back through the coupler tree. Assuming that the directional couplers are balanced and ideal, this approach presents excessive losses of approximately 3 * log2 (N) dB, where N is the number of branches of each coupler tree, when compared to an equivalent time multiplexed system. As a result of this, a signal-to-noise ratio can be obtained in the present mode when compared, for example, to the time division multiplexing mode illustrated in Figure 7.
    [0055] In another mode, coherence domain multiplexing can be used within the second multiplexing unit 9, which leaves the task of separating lateral lines for axial scanning of the interferometric system. Figure 9 illustrates the use of a coherence domain multiplexing unit 901 as an example of a second multiplexing unit 9 in conjunction with the first multiplexing system 17, according to one embodiment. This method uses directional coupler trees with delays in each branch, such that when the light reaches output waveguides 8, the various optical paths 10 accumulated a single delay for each output waveguide 8. In one example, the minimum spacing between the accumulated delays associated with the different output waveguides 8 is greater than the delay associated with the maximum sample depth from which optical contributions are expected.
    [0056] In one embodiment, combinations of any of the multiplexing techniques described above can be used within the second multiplexing unit 9. For example, frequency division multiplexing allows parallel reading, but is less efficient in terms of power supply optics, while time division multiplexing is best for conserving optical power. Figure 10 illustrates a multiplexing unit 1001 that combines both optical switches 2 and optical modulators 3. In this example, optical switches 2 are placed in the first path division while optical modulators 3 are used in the various other optical paths formed after the first division way.
    [0057] As mentioned earlier, optical switches 2 may not be ideal. This can lead to light leakage through optical paths that are different from the selected optical path 10. This can cause interference between independent lateral lines. The interference contribution may be less if optical switch 2 performs reasonably, because of the accumulation of non-active optical path suppression in backward and forward directions. In one example, optical modulators 3 can be included before each output waveguide 8, as illustrated in the multiplexing unit 1101 of Figure 11. Optical modulators 3 can be phase modulating elements that apply periodic excitation to displace the carrier of the interference pattern associated with each output waveguide 8 for a different frequency.
    [0058] In one embodiment, second multiplexing unit 9 may include independent scanning depth multiplexing units for each optical path. Figure 12 illustrates a combination of time division multiplexing units 1201 with an additional first multiplexing unit 17 included in each optical path. First multiplexing unit 17 can be implemented using one or more of the examples illustrated in Figures 4-6. In this mode, a single check depth can be chosen for each output waveguide 8, while the various optical paths are all multiplexed during a side scan.
    [0059] Due to factors such as the complexity of the integrated optical system, or the minimum spacing between the output waveguides 8 necessary to avoid coupling between them, it may be possible that adequate coverage of the lateral space for a scan cannot be achieved for a given set of design constraints. Thus, in another embodiment, the beams produced from each output waveguide 8 can be directed to cover the scanning space with sufficient density.
    [0060] Figure 13 illustrates an example including first multiplexing unit 17 and second multiplexing unit 9, in which the radiation beams produced from each output waveguide 8 can be directed to exit at the ends of the waveguides output 8 at a specific angle through beam targeting elements 12. Although a specific example of the second multiplexing unit 9 is shown in Figure 13, it should be understood that any other modality of the second multiplexing unit 9 can be used as well .
    [0061] A compromise can appear between the number of divisions using integrated optics and the side scan range of each output waveguide 8. In one embodiment, beam targeting elements 12 are electromechanical components that are integrated to exert a force over one or more output waveguides 8. This can increase the lateral scan interval of each output waveguide 8. Electromechanical elements 12 can be manufactured using, for example, microfabrication techniques and MEMS (Micro Electro Mechanical System) concepts ). In particular, using surface or volume micromachining, the output waveguides 8 can be mechanically released from the rest of the substrate, defining a movable structure (e.g., cantilever beam or the like). Electromechanical elements 12 may include a force application element based on, for example, an electrostatic attraction / repulsion, temperature expansion, piezoelectric principle or other suitable principle. In another example, outlet waveguides 8 can be manufactured in such a way as to induce a particular stress gradient in the main waveguide structure, for an inherent curvature in the cantilever profile after being released from the substrate. It should be understood that although output waveguides 8 are illustrated in Figure 13 to have a given curvature, this is only an example and should not be considered as limiting.
    [0062] According to one modality, the movement of the output waveguides 8 can be either in the lateral scanning plane or in a plane perpendicular to it. As such, it is possible to obtain a 3D image without moving elements external to the integrated optical substrate, since the side scan is performed by multiplexing the optical paths associated with different output waveguides 8, and the vertical scan is achieved by moving outgoing wave 8 out of the plane or otherwise directing the light beam passing through outgoing plane waveguides 8.
    [0063] Figure 14 illustrates an example of scanning system 116 including first multiplexing unit 17 and second multiplexing unit 9. Scanning system 116 also incorporates an optical focusing element 4. In the mode shown, second multiplexing unit 9 uses time division multiplexing. However, the second multiplexing unit 9 can also use any of the other techniques, or any combinations of techniques, discussed earlier. In one embodiment, optical element 4 includes a single lens, but one skilled in the art will understand that any number of lenses can be used to achieve the desired focusing effect. A plurality of radiation beams are shown. All beams can be activated at the same time, as in the case of the frequency division multiplexing system. Alternatively, only a part of the beams are activated in the case of a time division multiplexing system. In one embodiment, the spacing and side band of the output waveguide matrix 8 are adjusted to the magnification specifications of the optical element 4 and any potential sample specifications. In one embodiment, the distance between adjacent beams corresponding to the different output waveguides 8 is small enough in relation to the diameter of the beams, so that the information collected along the adjacent beams can be rearranged later as a two-dimensional or three-dimensional processed image. Sample. In one example, the distance between adjacent beam centers is within 1-10 times the diameter of a single beam, when both the distance and this diameter are measured in the focal plane of the optical element 4. The definition of Maximum Medium Width Total (FWHM) can be used, for example, to determine the diameter of the radiation beam.
    [0064] Figure 15 illustrates another example of scanning system 116 that includes a combined multiplexing unit 1501 together with a first multiplexing unit 17 incorporated into each output. Similar to Figure 12, a single check depth can be defined for each output using multiplexing units 17. In one example, combined multiplexing unit 1501 includes optical switches 2 to select a subset (either 13 'or 13 ") of active optical paths. Optical modulators 3 are also included for multiplexing paths in the selected subset 13 ', 13 "of active optical paths, allowing simultaneous measurement of light contributions that were dispersed by the sample and collected by various output waveguides 8 First multiplexing units 17 operate independently on each of the selected optical paths associated with each output waveguide 8, allowing independent control of the scanning depth for each output.
    [0065] In order to direct the beams associated with various subsets 13 ', 13 ", optical focusing elements 1502 are included downstream of the output waveguides 8. In one embodiment, optical focusing elements 1502 include a plurality of lenses as illustrated to focus the beams associated with a given subset in the same region as the target sample. For example, optical focusing elements 1502 include a single large lens and a plurality of smaller lenses, with each smaller lens configured to collect radiation beams from each subset 13 ', 13 ". Although only two subsets 13 ', 13 "of optical paths are illustrated, it should be understood that any number of subsets can be generated through combined multiplexing unit 1501. In one embodiment, the various beams of a given subset are considered to be directed to the same target region in the sample when the distance between the centers of each beam in the subset is less than or equal to twice the diameter of each beam, when both the distance and this diameter are measured in the focal plane associated with optical focusing elements 1502. The definition of Maximum Full Width Medium (FWHM) can be used, for example, to determine the diameter of the radiation beam.The illustrated modality allows the measurement of the sample with spatial diversity, for example, measuring the same region of the sample from different directions. This reduces noise in the image.
    [0066] The modality in Figure 15 allows to obtain information about the angular dependence of the sample dispersion function, since it is possible to measure the light that is scattered over a sample region in different directions in relation to the direction of the incident light . For example, when one of the beams produced from an output waveguide 8 reaches the sample, part of the light will be scattered in different directions. The light that is scattered backwards in relation to the incident light is redirected by optical focusing elements 1502 back to the original output waveguide 8. However, according to one embodiment, optical focusing elements 1502 are configured to direct the beams of a given subset 13 ', 13 "in the direction of the same sample region. Therefore, light scattered in directions other than directly backwards (in relation to incident light) can be directed by optical focusing elements 1502 towards one of the others output waveguides 8 belonging to subset 13 ', 13 ". The total path length traveled by the light from the point where it exits the device through an output waveguide 8 until it is collected by a different output waveguide 8, belonging to the same subset 13 ', 13 ", is different for each output waveguide 8 belonging to subset 13 ', 13 ". In one embodiment, this difference in path length is accounted for through the adjustable scanning depth range on each optical path using the first multiplexing unit 17. As such, this mode allows simultaneous measurement of scattered light in different directions for the same region. sample in a single interferometer, and the angular dependence of the sample dispersion function can be obtained.
    [0067] Figure 16 illustrates an example technique for scanning a sample both axially and laterally, according to a modality. The beams are represented in the geometric optical approximation by two lines corresponding to the lateral extension of the optical energy. The lines cross each other in a first approximation in a focal plane 1601. Axial scanning is performed using the OCT interferometric system described here with the multiplication of the basic scanning range in multiplexed bands (for example, by using frequency division multiplexing) . The diagonal lines that cross in pairs represent beams of light that correspond to each output waveguide 8, after focusing on the sample. The intersection points define focal plane 1601 associated with the lens system used. Laterally, time division, frequency division, or any other type of multiplexing is performed between the optical paths, as explained in the previous modalities. Axially, frequency division multiplexing can be chosen to select the scanning depth in order to multiply the effect of the reference arm of an interferometry system. Thus, in modalities, a check is made only within a specified section for a given frequency range (for example, f, 2f, 3f, etc., as shown in Figure 16).
    [0068] Another mode of scanning system 116 is illustrated in Figure 17. In one mode, a gradient index lens (GRIN) 1701 is included to focus the light from the output waveguides 8 to a sample. GRIN 1701 lens can be mounted contiguously to the same substrate associated with optical waveguides 8, or in a cavity engraved on the substrate, where the various integrated waveguides are produced due to their compact size and substantially cylindrical shape. In another example, GRIN 1701 lens is monolithically integrated on the same substrate as output waveguides 8. The more compact assembly allows the scanning system to be encapsulated with biocompatible materials and ready for sterilization for the production of a medical sampling element, according to a modality. The medical sampling element can be inserted into a catheter, needle, or any other small sized medical device or instrument, for the study of small tissues in areas that are typically difficult to access. As previously discussed in relation to other focusing elements, the distance between corresponding adjacent beams for different output waveguides 8 is sufficiently small in relation to the diameter of the beams, so that the information collected along the adjacent beams can be rearranged more later as a two-dimensional or three-dimensional processed image of the sample. In one example, the distance between adjacent beam centers is within 1-10 times the diameter of a single beam, when both the distance and this diameter are measured in the focal plane of the GRIN 1701 lens. The definition of Maximum Medium Width Total (FWHM) can be used, for example, to determine the diameter of the radiation beam.
    [0069] Figures 18A-B illustrate a top and side view, respectively, of the scanning system 116, according to an embodiment. In this embodiment, scanning system 116 includes a reflection element 5 positioned downstream of the GRIN 1701 lens. In one example, the reflection element 5 is a right-angle prism, as illustrated in Figure 18B. In this example, the reflection element 5 can direct one or more incoming radiation beams in a direction perpendicular to the initial beam direction from the output waveguides 8. In one embodiment, scanning system 116 as incorporated in Figure 18A can be mounted on a catheter, where small movements of the device along a guide wire can be used to provide 3D processing of a blood vessel wall under study. Reflection element 5 can be a separate component from the rest of the scanning system 116. Alternatively, reflection element 5 can be integrated into the same substrate either as output waveguides 8 or GRIN lens 1701. In another example, all elements illustrated can be monolithically integrated on the same substrate.
    [0070] Figures 19A-B illustrate a top and side view, respectively, of the scanning system 116, according to an embodiment. In this embodiment, scanning system 116 includes an adjustable reflection element 6 positioned downstream of the GRIN 1701 lens. In one example, the adjustable reflection element 6 is a mechanically adjustable reflector. The inclusion of the adjustable reflection element 6 allows the generation of 3D images with a single low-speed scanning axis, instead of having two. In effect, the need to provide a high-speed scan of the sample is removed in such a mode, serving only to guide the bundle group to the scanning area, or to provide the slow direction in a three-dimensional scan. Thus, to generate 3D images, only a single low-speed scanning axis is needed, instead of two, according to one modality. Adjustable reflection element 6 can adjust the reflected angle of the radiation input beams by any suitable means, as will be known to a person skilled in the relevant art (s). For example, adjustable reflection element 6 can use coupled piezoelectric actuators or electrostatic drive, or mechanical rotation to adjust the orientation of the adjustable reflection element 6.
    [0071] Figures 20A-B illustrate a top and side view, respectively, of the scanning system 116, according to an embodiment. In this mode, scanning system 116 includes an adjustable reflector matrix 2001. Adjustable reflector matrix 2001 can be used to scan several images of different target regions of a sample. In one embodiment, each beam of radiation produced is associated with a reflection element in the adjustable reflector matrix 2001. Each element can be moved individually to change the reflection angle of the associated incoming radiation beam. This allows for a situation where each beam of radiation is directed at a different region of a sample.
    [0072] In one embodiment, the adjustable reflector matrix 2001 includes MEMS devices such as adjustable micro mirrors. Micro mirrors can be manufactured using conventional microfabrication techniques and integrated on the same substrate either as output waveguides 8 or GRIN 4 lens. In another embodiment, adjustable reflector matrix 2001 can be manufactured on a separate substrate and connected by "flip" -chip "to the substrate that includes output waveguides 8 and GRIN lens 4. If each of the reflection elements in the adjustable reflector matrix 2001 provides independent cross-scan, then the scanning system is capable of, for example, obtaining a large number of images either sequentially or simultaneously.
    [0073] It should be understood that for the modalities described above, the use of GRIN 1701 lens can be replaced by other optical focusing elements suitable to achieve the same result. In addition, although the second multiplexing unit 9 is illustrated in the modalities shown in Figures 17-20 as using time division multiplexing, it should be understood that any multiplexing technique, or a combination of techniques, as described above, also could be used.
    [0074] Although the above modalities have been described in the context of an OCT system, any of the various modalities described above can also be applied to other applications. For example, any of the various modalities described above can be applied for the optical reading of data stored in optical multilayer systems, in which the selection between layers is performed by the detection systems based on an optical coherence propagation. An advantage provided for example, in this case, is the increase in the reading speed, when the reading is (almost) simultaneous with a large number of optical tracks. It is also to be noted that any of the modalities described above is susceptible to changes in details, as long as they do not alter the fundamental principle and essence of the invention.
    [0075] Figure 21 illustrates an example method 2100 for performing lateral scanning, according to a modality. Method 2100 can be performed, for example, by any of the various modalities described above for the scanning system 116.
    [0076] In step 2102, a radiation beam is received in a first multiplexing unit. The first multiplexing unit can be, for example, any of the multiplexing units described in relation to Figures 4-6.
    [0077] In step 2104, a group delay is introduced for the radiation beam received in the first multiplexing unit based on an optical path traveled by the radiation beam received in the first multiplexing unit between a first plurality of optical waveguides in the first multiplexing unit. Group delay can be introduced in a variety of ways, such as using waveguide segments of different lengths or waveguide segments allowing modification of the refractive index by effects such as thermo-optical, electro-optical, injection loading, etc. In one example, optical modulation elements and / or optical switches are used to differentiate between the beam from a plurality of paths, with each path having a unique group delay associated with it.
    [0078] In step 2106, a radiation beam is received by a second multiplexing beam unit. The radiation beam received by the second multiplexing unit can be the same radiation beam received by the first multiplexing unit, for example, when the first multiplexing unit is located in the sample arm. Alternatively, the radiation beam received by the second multiplexing unit can be different from the radiation beam received by the first multiplexing unit, for example, when the first multiplexing unit is located on the reference arm. The second multiplexing unit can be, for example, any of the various multiplexing units described in relation to Figures 7-13 or Figure 15.
    [0079] In step 2108, the radiation beam received by the second multiplexing unit is differentiated between a second plurality of optical waveguides to produce one or more output radiation beams. The radiation beam received by the second multiplexing unit can be differentiated between a variety of optical paths using either one, or a combination of time division multiplexing, frequency division multiplexing, coherence domain multiplexing, etc.
    [0080] In step 2110, the one or more outgoing radiation beams are oriented towards a sample. Guidance can include focusing and / or reorienting the light, as described in the modalities illustrated, for example, in Figures 14-15 and Figures 17-20.
    [0081] It is to be appreciated that the Detailed Description section, and not the Summary and Summary sections, is intended to be used to interpret the claims. The Summary and Summary sections may establish one or more, but not all exemplary embodiments of the present invention, as contemplated by the inventor (s), and therefore are not intended to limit the present invention and the appended claims. in any way.
    [0082] Modalities of the present invention have been described above with the aid of functional building blocks that illustrate the implementation of specified functions and relationships thereof. The limits of these functional building blocks have been defined here arbitrarily for convenience of the description. Alternative limits can be defined as long as their specified functions and relationships are properly performed.
    [0083] The previous description of the specific modalities will reveal so completely the general nature of the invention that others can, by applying knowledge within the skill of the technique, readily modify and / or adapt such specific modalities for various applications, without excessive experimentation, without depart from the general concept of the present invention. Therefore, these adaptations and modifications are intended to be within the meaning and range of equivalents of the revealed specifications, based on the teachings and guidelines presented here. And to be understood that the phraseology or terminology used here is for the purpose of description and not limitation, such that the terminology or phraseology of the present specification must be interpreted by the technician experienced in the light of the teachings and guidance.
    [0084] The breadth and scope of the present invention should not be limited by any of the exemplary modalities described above, but should be defined only in accordance with the following claims and their equivalents.
    权利要求:
    Claims (37)
    [0001]
    1. Low coherence interferometry system, characterized by the fact that it comprises: a first multiplexing unit configured to receive a first beam of radiation and comprising a first plurality of optical delay elements configured to introduce a group delay for the first beam of radiation based on an optical path traveled by the first beam of radiation between a first plurality of optical waveguides, and a second multiplexing unit configured to receive a second beam of radiation and comprising a second plurality of optical modulators configured to differentiate the second radiation beam between a second plurality of optical waveguides for the production of one or more outgoing radiation beams, wherein the second plurality of optical waveguides is configured to orient the one or more outgoing radiation beams towards to a sample.
    [0002]
    2. Low coherence interferometry system, according to claim 1, characterized by the fact that the first multiplexing unit also comprises a plurality of switches configured to select the optical path traveled by the radiation beam between the first plurality of guides of optical wave.
    [0003]
    3. Low coherence interferometry system, according to claim 1, characterized by the fact that the first multiplexing unit further comprises a plurality of phase modulators.
    [0004]
    4. Low coherence interferometry system, according to claim 1, characterized by the fact that the second multiplexing unit is configured to receive the second beam of radiation from a single output of the first multiplexing unit.
    [0005]
    5. Low coherence interferometry system, according to claim 1, characterized by the fact that the second multiplexing unit is configured to receive the second radiation beam from one of the two outputs of the first multiplexing unit.
    [0006]
    6. Low coherence interferometry system, according to claim 1, characterized by the fact that it also comprises an optical element disposed between the second multiplexing unit and the sample.
    [0007]
    7. Low coherence interferometry system, according to claim 6, characterized by the fact that the optical element is a single lens.
    [0008]
    8. Low coherence interferometry system, according to claim 7, characterized by the fact that the single lens is configured to focus the one or more beams of output radiation in a focal plane in such a way that a distance between the centers of the adjacent beams in the focal plane is between 1 and 10 times larger than the diameter of one of the beams in the focal plane.
    [0009]
    9. Low coherence interferometry system according to claim 7, characterized by the fact that it also comprises a plurality of lenses, each smaller than the single lens, configured to focus at least a subset of the one or more beams of output radiation to a first target region of the sample and at least focus on another subset of the one or more beams of output radiation to a second target region of the sample.
    [0010]
    10. Low coherence interferometry system, according to claim 6, characterized by the fact that the optical element is a gradient index lens (GRIN).
    [0011]
    11. Low coherence interferometry system, according to claim 6, characterized by the fact that it also comprises a reflector arranged downstream of the optical element and configured to change a direction of propagation of the one or more outgoing radiation beams.
    [0012]
    12. Low coherence interferometry system according to claim 11, characterized by the fact that the altered direction of propagation is substantially perpendicular to an initial direction of propagation.
    [0013]
    13. Low coherence system, according to claim 11, characterized by the fact that an orientation of the reflection element is adjustable, such that an angle of change for the direction of propagation of the one or more radiation beams outgoing it is adjustable.
    [0014]
    14. Low coherence interferometry system, according to claim 13, characterized by the fact that the adjustable reflector comprises microelectromechanical components.
    [0015]
    15. Low coherence interferometry system according to claim 1, characterized by the fact that the second plurality of optical modulators comprises phase modulators.
    [0016]
    16. Low coherence interferometry system according to claim 1, characterized in that the second plurality of optical modulators comprises elements of optical delay.
    [0017]
    17. Low coherence interferometry system according to claim 1, characterized by the fact that the second plurality of optical modulators comprises optical switches.
    [0018]
    18. Low coherence interferometry system, according to claim 1, characterized by the fact that the group delay is associated with a scanning depth of the sample and is carried out through one or more radiation beams at the second unit multiplexing.
    [0019]
    19. Low coherence interferometry system, according to claim 1, characterized by the fact that the second plurality of optical waveguides is further configured to collect scattered radiation from the sample.
    [0020]
    20. Low coherence interferometry system, according to claim 1, characterized by the fact that the first plurality of optical waveguides and the second plurality of optical waveguides are integrated on the same substrate.
    [0021]
    21. Low coherence interferometry system, according to claim 1, characterized by the fact that it also comprises microelectromechanical actuators configured to bend one or more of the second plurality of optical waveguides.
    [0022]
    22. Low coherence interferometry system according to claim 1, characterized by the fact that the second radiation beam is different from the first radiation beam.
    [0023]
    23. Low coherence interferometry system according to claim 22, characterized by the fact that the first multiplexing unit is located in a reference arm of the low coherence interferometry system and the second multiplexing unit is located in a sample arm of the low coherence interferometry system.
    [0024]
    24. Low coherence interferometry system according to claim 1, characterized by the fact that the second radiation beam is the same as the first radiation beam.
    [0025]
    25. Low coherence interferometry system according to claim 24, characterized in that the first multiplexing unit and the second multiplexing unit are both located on a sample arm of the low coherence interferometry system.
    [0026]
    26. Method performed by a low coherence interferometry system, characterized by the fact that it comprises: receiving a beam of radiation in a first multiplexing unit; introducing a group delay for the first radiation beam received in the first multiplexing unit based on an optical path traveled by the first radiation beam received in the first multiplexing unit between a first plurality of optical waveguides in the first multiplexing unit; receiving a second beam of radiation in a second multiplexing unit; differentiating the second beam of radiation received in the second multiplexing unit between a second plurality of optical waveguides for producing one or more outgoing radiation beams; and directing the one or more beams of output radiation to a sample.
    [0027]
    27. Method according to claim 26, characterized in that it further comprises modulating a phase of the first radiation beam in the first multiplexing unit.
    [0028]
    28. Method according to claim 26, characterized in that the differentiation of the second radiation beam comprises the introduction of a delay for the second radiation beam.
    [0029]
    29. Method according to claim 26, characterized in that the differentiation of the second beam of radiation comprises switching the second beam of radiation between the second plurality of optical waveguides.
    [0030]
    30. Method according to claim 26, characterized by the fact that the differentiation of the radiation beam comprises the modulation of the phase of the second radiation beam.
    [0031]
    31. Method, according to claim 26, characterized by the fact that it further comprises the focusing of the one or more beams of output radiation through an optical element.
    [0032]
    32. Method, according to claim 31, characterized by the fact that it also comprises the alteration of a direction of propagation of the one or more beams of outgoing radiation by means of a reflector disposed downstream of the optical element.
    [0033]
    33. The method of claim 26, characterized by the fact that it further comprises folding one or more of the second plurality of optical waveguides through microelectromechanical actuators.
    [0034]
    34. Method, according to claim 26, characterized by the fact that it also comprises collection of scattered radiation from the sample.
    [0035]
    35. Method according to claim 26, characterized in that the second multiplexing unit receives the second radiation beam from the first multiplexing unit.
    [0036]
    36. Method according to claim 26, characterized in that the second radiation beam received in the second multiplexing unit is the same as the first radiation beam received in the first multiplexing unit.
    [0037]
    37. Method according to claim 26, characterized in that the second radiation beam received in the second multiplexing unit is different from the first radiation beam received in the first multiplexing unit.
    类似技术:
    公开号 | 公开日 | 专利标题
    BR112013029785B1|2021-01-05|low coherence interferometry system and method performed by a low coherence interferometry system
    US10533837B2|2020-01-14|Multichannel optical receivers
    US6501551B1|2002-12-31|Fiber optic imaging endoscope interferometer with at least one faraday rotator
    US6134003A|2000-10-17|Method and apparatus for performing optical measurements using a fiber optic imaging guidewire, catheter or endoscope
    JP2014237042A|2014-12-18|Construction, apparatus, endoscope, catheter and method for performing optical image generation by irradiating a plurality of spots on sample simultaneously and detecting the same
    KR102326133B1|2021-11-15|Common-path integrated low coherence interferometry system and method therefor
    JP2013006071A|2013-01-10|Equipment configured so as to propagate one or more electromagnetic radiation
    WO1997032182A9|1998-12-10|Method and apparatus for performing optical measurements using a fiber optic imaging guidewire, catheter or endoscope
    US10113856B2|2018-10-30|Line-field imaging systems and methods incorporating planar waveguides
    WO1999049780A1|1999-10-07|Optical coherence domain reflectometry guidewire
    CN103181754A|2013-07-03|Method and apparatus for performing optical imaging using frequency-domain interferometry
    BR112013033529A2|2020-06-02|INTEGRATED DELAY LINE FOR OPTICAL COHERENCE TOMOGRAPHY
    ES2885867T3|2021-12-15|Distributed delay line for low coherence interferometry
    JP2013025252A|2013-02-04|Light source device and imaging apparatus using the same
    Wu et al.2016|Extending the effective imaging depth in spectral domain optical coherence tomography by dual spatial frequency encoding
    KR101345788B1|2014-01-16|High resolution optical coherence tomography using wavelength division multiplexing coupler| and wide band splitter
    Sun2012|MEMS based optical coherence tomography imaging
    Piyawattanametha2012|Dual Axes Confocal Microendoscope
    同族专利:
    公开号 | 公开日
    CN103688133B|2017-03-01|
    EP2710327A1|2014-03-26|
    BR112013029785A2|2017-01-17|
    EP2710327B1|2021-10-13|
    JP2014517286A|2014-07-17|
    CN103688133A|2014-03-26|
    US9354040B2|2016-05-31|
    US20140078510A1|2014-03-20|
    ES2415555B2|2014-07-09|
    ES2415555A1|2013-07-25|
    CA2836609C|2017-11-21|
    WO2012160005A1|2012-11-29|
    CA2836609A1|2012-11-29|
    JP6118796B2|2017-04-19|
    AU2012260954B2|2015-06-18|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    WO1998043068A1|1997-03-26|1998-10-01|Kowa Company, Ltd.|Optical measuring instrument|
    JPH10267830A|1997-03-26|1998-10-09|Kowa Co|Optical measuring device|
    US6865311B2|2001-11-02|2005-03-08|Oplink Communications, Inc.|Re-configurable dispersion compensation module |
    US7474407B2|2003-02-20|2009-01-06|Applied Science Innovations|Optical coherence tomography with 3d coherence scanning|
    RU2247938C1|2003-05-27|2005-03-10|Геликонов Валентин Михайлович|Optical device for object analysis|
    JP4505807B2|2004-08-09|2010-07-21|国立大学法人筑波大学|Multiplexed spectral interferometric optical coherence tomography|
    WO2006058346A1|2004-11-29|2006-06-01|The General Hospital Corporation|Arrangements, devices, endoscopes, catheters and methods for performing optical imaging by simultaneously illuminating and detecting multiple points on a sample|
    US7414728B2|2004-12-23|2008-08-19|Massachusetts Institute Of Technology|Reconfigurable polarization independent interferometers and methods of stabilization|
    US20080108867A1|2005-12-22|2008-05-08|Gan Zhou|Devices and Methods for Ultrasonic Imaging and Ablation|
    US7488930B2|2006-06-02|2009-02-10|Medeikon Corporation|Multi-channel low coherence interferometer|
    CA2675890A1|2007-01-19|2008-07-24|University Health Network|Electrostatically driven imaging probe|
    US7873286B2|2007-10-19|2011-01-18|Ciena Corporation|Optical receiver systems and methods for polarization demultiplexing, PMD compensation, and DXPSK demodulation|
    US8018597B2|2008-06-20|2011-09-13|Com Dev International Ltd.|Slab waveguide spatial heterodyne spectrometer assembly|
    JP5645445B2|2009-05-22|2014-12-24|キヤノン株式会社|Imaging apparatus and imaging method|
    CN101715153B|2009-12-02|2013-07-17|华中科技大学|Hybrid wavelength-division and time-division multiplexing passive sensing optical network|
    US9164240B2|2011-03-31|2015-10-20|Lightlab Imaging, Inc.|Optical buffering methods, apparatus, and systems for increasing the repetition rate of tunable light sources|
    US8655431B2|2011-05-31|2014-02-18|Vanderbilt University|Apparatus and method for real-time imaging and monitoring of an electrosurgical procedure|ES2396784B2|2011-03-15|2014-07-23|Medlumics, S.L.|INTEGRABLE ACTIVE EQUALIZATION SYSTEM OF CHROMATIC DISPERSION.|
    EP2690395A1|2012-07-24|2014-01-29|Hexagon Technology Center GmbH|Interferometric distance measuring assembly and method|
    US9400169B2|2012-12-06|2016-07-26|Lehigh University|Apparatus and method for space-division multiplexing optical coherence tomography|
    EP2929288A4|2012-12-06|2016-07-06|Univ Lehigh|Space-division multiplexing optical coherence tomography apparatus|
    US10660526B2|2012-12-31|2020-05-26|Omni Medsci, Inc.|Near-infrared time-of-flight imaging using laser diodes with Bragg reflectors|
    CA2895969A1|2012-12-31|2014-07-03|Omni Medsci, Inc.|Near-infrared lasers for non-invasive monitoring of glucose, ketones, hba1c, and other blood constituents|
    US9164032B2|2012-12-31|2015-10-20|Omni Medsci, Inc.|Short-wave infrared super-continuum lasers for detecting counterfeit or illicit drugs and pharmaceutical process control|
    WO2014143276A2|2012-12-31|2014-09-18|Omni Medsci, Inc.|Short-wave infrared super-continuum lasers for natural gas leak detection, exploration, and other active remote sensing applications|
    CA2895982A1|2012-12-31|2014-07-03|Omni Medsci, Inc.|Short-wave infrared super-continuum lasers for early detection of dental caries|
    WO2014113506A1|2013-01-15|2014-07-24|Magic Leap, Inc.|Ultra-high resolution scanning fiber display|
    US9835436B2|2013-11-01|2017-12-05|Tomey Corporation|Wavelength encoded multi-beam optical coherence tomography|
    US9200888B2|2013-11-01|2015-12-01|Tomey Corporation|Multi-channel optical coherence tomography|
    US20150133778A1|2013-11-04|2015-05-14|Medlumics S.L.|Diagnostic Device for Dermatology with Merged OCT and Epiluminescence Dermoscopy|
    US10835313B2|2014-01-30|2020-11-17|Medlumics S.L.|Radiofrequency ablation catheter with optical tissue evaluation|
    US10206584B2|2014-08-08|2019-02-19|Medlumics S.L.|Optical coherence tomography probe for crossing coronary occlusions|
    US9976844B2|2015-02-06|2018-05-22|Medlumics S.L.|Miniaturized OCT package and assembly thereof|
    EP3106828A1|2015-06-16|2016-12-21|Academisch Medisch Centrum|Common-path integrated low coherence interferometry system and method therefor|
    US9869541B2|2015-07-22|2018-01-16|Medlumics S.L.|High-speed optical coherence tomography using multiple interferometers with suppressed multiple scattering cross-talk|
    US10194981B2|2015-07-29|2019-02-05|Medlumics S.L.|Radiofrequency ablation catheter with optical tissue evaluation|
    US10113858B2|2015-08-19|2018-10-30|Medlumics S.L.|Distributed delay-line for low-coherence interferometry|
    WO2017205892A1|2016-06-01|2017-12-07|The Australian National University|Improvements in optical delay lines|
    DE102016218290A1|2016-07-15|2018-01-18|Carl Zeiss Meditec Ag|Method for the highly sensitive measurement of distances and angles in the human eye|
    EP3516325B1|2016-09-26|2021-12-15|Ixa Amc Office / Academic Medical Center|Single-chip optical coherence tomography device|
    KR102227571B1|2016-09-26|2021-03-15|아이엑스에이 에이엠씨 오피스 / 아카데미쉬 메디쉬 센트럼|High-resolution integrated optics-based spectrometer|
    US10786389B2|2016-10-26|2020-09-29|Amo Development, Llc|Ophthalmic laser delivery apparatus using MEMS micromirror arrays for scanning and focusing laser beam|
    CN111212592A|2017-05-12|2020-05-29|周超|Spatial division multiplexing optical coherence tomography using integrated photonic devices|
    US10982947B2|2017-06-12|2021-04-20|Sightline Innovation Inc.|System and method of surface inspection of an object using mulitplexed optical coherence tomography|
    US10648797B2|2017-11-16|2020-05-12|Quality Vision International Inc.|Multiple beam scanning system for measuring machine|
    WO2019123662A1|2017-12-22|2019-06-27|オリンパス株式会社|Bioinstrumentation device, bioinstrumentation system, and bioinstrumentation method|
    US10820806B2|2017-12-27|2020-11-03|Medlumics S.L.|Bi-refringence compensated waveguides|
    WO2019183838A1|2018-03-28|2019-10-03|深圳市太赫兹科技创新研究院|Optical coherence tomography system|
    US10509167B2|2018-04-23|2019-12-17|Hewlett Packard Enterprise Development Lp|Optical phase difference calculation using analog processing|
    US20190380589A1|2018-06-18|2019-12-19|Medlumics S.L.|Catheter with merged optical tissue evaluation and laser ablation|
    CN109620131B|2018-12-14|2021-08-03|佛山科学技术学院|Common-path micro-lens array multi-beam optical coherence elasticity measurement system and method|
    法律状态:
    2018-12-11| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2020-01-14| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2020-04-28| B25G| Requested change of headquarter approved|Owner name: MEDLUMICS, S.L. (ES) |
    2020-10-27| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-01-05| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 18/05/2012, OBSERVADAS AS CONDICOES LEGAIS. |
    优先权:
    申请号 | 申请日 | 专利标题
    ES201130818|2011-05-20|
    ES201130818A|ES2415555B2|2011-05-20|2011-05-20|SWEEP DEVICE FOR LOW COHERENCE INTERFEROMETRY.|
    PCT/EP2012/059308|WO2012160005A1|2011-05-20|2012-05-18|Scanning device for low coherence interferometry|
    [返回顶部]