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HOLOGRAPHIC MICROSCOPE, HOLOGRAPHIC IMAGE GENERATION METHOD, AND METHOD FOR ACQUIRING DATA FOR HOLOGRAPHIC IMAGE 新技術説明会

外国特許コード F140008036
整理番号 S2012-1233-C0
掲載日 2014年11月19日
出願国 世界知的所有権機関(WIPO)
国際出願番号 2013JP077059
国際公開番号 WO 2014054776
国際出願日 平成25年10月4日(2013.10.4)
国際公開日 平成26年4月10日(2014.4.10)
優先権データ
  • 特願2012-223690 (2012.10.5) JP
発明の名称 (英語) HOLOGRAPHIC MICROSCOPE, HOLOGRAPHIC IMAGE GENERATION METHOD, AND METHOD FOR ACQUIRING DATA FOR HOLOGRAPHIC IMAGE 新技術説明会
発明の概要(英語) In the present invention, a tomographic image can be accurately generated at high speed in a holographic microscope, a holographic (tomographic) image generation method, and a method for acquiring data for a holographic (tomographic) image. The present method includes a data acquisition process (S1) and a tomographic image generation process (S2 through S7). In the data acquisition process, holograms (IjOR, IjQR, IjLR) of object light (O) and so forth are acquired for each light with a wavelength (λj) by changing the wavelengths of the illumination light (Q), off-axis spherical wave reference light (R), and inline spherical wave reference light (L). In the tomographic image generation process, a reproduced light wave (hj) of the object light (Oj) and a reproduced light wave (cj) of the illumination light (Qj) on a reproduced surface (z = zP) are acquired from these holograms. A reproduced light wave (hj / (cj / |cj|) with adjusted phase is added for each wavelength (j = 1, ⋅ ⋅, N) to acquire a tomographic hologram (HP). From this, a focused tomographic image SP = |HP|2 which is accurate without distortion can be acquired.
従来技術、競合技術の概要(英語) BACKGROUND ART
Conventionally, optical coherence tomography (OCT: Optical, coherence, tomography) techniques, harmless to human body-the-art non-invasive medical diagnosis and technology, research and development of an apparatus application to a living body measuring device has been actively researched. The OCT, light from the surface of the object to a depth that can be entered, to obtain information about the structure of the optical response of the object in the art, are used in applications such as fundus examination. Initially proposed OCT is put to practical use, the spot size of the beam is to use the laser light. The laser beam is separated into illumination light and the reference light, the illumination light is incident into an object, is reflected back from the object and the light that is transmitted by the interference of the reference light is observed. The object from the interference observed in the reflection position of light and reflection intensity information that is the light traveling direction (longitudinal or depth direction) of the structure of the object in the derived information. The laser beam incident position on the surface of the object 1 is moved two-dimensionally obtained tomographic image of the surface 1, 2 for transfer to a three-dimensional object 3 and the resulting three-dimensional structure data, any tomographic image data from the tomographic plane can be reproduced. Incidentally, since the tomographic image, a layer having a thickness in the thickness direction of a finite average light reflection intensity distribution of the surface. 1 A layer having a thickness such that as the surface (e.g. layer center plane) when used as a representative, a typical surface referred to as the surface of the slice plane or reproduction.
OCT is, to derive information of the vertical direction depending on a manner of being classified into 2. 1 Light pulse time of flight of the two time-domain OCT (TD-OCT) to directly obtain and, in the vertical direction 1 of the other one of the difference in the distance from a spatial frequency of interference fringes obtained in the Fourier domain OCT (FD-OCT) is. TD-OCT interference of the light waves of the former is processed in the real space (time domain). TD-OCT is, the first OCT and put to practical use, 1 of the illumination light 1 in the depth direction by irradiation at a time point information are obtained. Therefore, the depth direction by the TD-OCT obtaining information of each point, change the optical path length of the reference light is needed, therefore in the light path of the reference mirror is moved mechanically. FD-OCT interference of the light waves of the latter is in the Fourier space (frequency or wavelength region) treatment. FD-OCT is, further, the fixed wavelength light source and the spectroscope is used (SD-OCT) OCT and the spectral region, to change the oscillation wavelength of the light source-OCT(SS-OCT) the wavelength-divided into a display. FD-OCT of the, the mechanical movement of the reference mirror is not necessary, to achieve the high-speed imaging.
However, any of the FD-OCT also, because of the use of laser light of the beam spot size, 2 or 3 in order to obtain a three-dimensional data two-dimensional scanning a galvanometer, the reference mirror and the light from the interferometer along the surface of the object at which the movable head 1 is mechanically or 2 two-dimensionally or two-dimensionally scanning the need to, the imaging speed is limited. On the other hand, does not require mechanical scanning of the optical system as an imaging method, the imaging lens and the optical wavelength swept laser light is used by the tomographic imaging method is digital holography has been proposed (for example, see Non-Patent Document 1). In addition, the tomographic imaging method is applied to the biological tissue has been reported (for example, see Non-Patent Document 2). These non-patent document 1, 2 in the tomographic imaging method described in, the plane wave light of the wavelength sweep is used as illumination light, the object light is recorded in the hologram for each wavelength. For a hologram recording at each wavelength, a reproduction position at a common phase of the object light in each wavelength is obtained, each of the hologram at each phase of the object beam is obtained and then normalized by adding each hologram with each other, and the reproduced at the position where the hologram for reproducing the image is obtained. At other positions on the tomographic image is, for the tomographic image recorded on the hologram obtained by the propagating light waves.
Is digital holography, as a method of capturing and recording a high speed has been developed. For example, the spatial heterodyne modulation off-axis holography apply filtering the spatial frequency of the broadband complex amplitude holograms can be recorded on the high speed and accurately one-shot digital holography has been proposed (for example, see Patent Document 1). In addition, to solve the problem of the conventional optical microscope, using this one-shot digital holography, the holographic microscope, a small hologram of the object in the image recording method, a method for making a hologram for reproducing the high resolution image, and the image reproducing method has been proposed (for example, see Patent Document 2). The microscope, and a transmission type and the reflection-type microscope, the microscope and the imaging lens is not used lens-less holographic, conventional media or an imaging lens to solve the problem of the influence of the optical microscope. That is, the microscope, by not using the imaging lens, the object light of a large numerical aperture of the one-shot 3 with a high resolution and accurate distortion-free three-dimensional moving image can be reproduced using a computer.
  • 出願人(英語)
  • ※2012年7月以前掲載分については米国以外のすべての指定国
  • UNIVERSITY OF HYOGO
  • 発明者(英語)
  • SATO, Kunihiro
国際特許分類(IPC)
指定国 National States: AE AG AL AM AO AT AU AZ BA BB BG BH BN BR BW BY BZ CA CH CL CN CO CR CU CZ DE DK DM DO DZ EC EE EG ES FI GB GD GE GH GM GT HN HR HU ID IL IN IR IS JP KE KG KN KP KR KZ LA LC LK LR LS LT LU LY MA MD ME MG MK MN MW MX MY MZ NA NG NI NO NZ OM PA PE PG PH PL PT QA RO RS RU RW SA SC SD SE SG SK SL SM ST SV SY TH TJ TM TN TR TT TZ UA UG US UZ VC VN ZA ZM ZW
ARIPO: BW GH GM KE LR LS MW MZ NA RW SD SL SZ TZ UG ZM ZW
EAPO: AM AZ BY KG KZ RU TJ TM
EPO: AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR
OAPI: BF BJ CF CG CI CM GA GN GQ GW KM ML MR NE SN TD TG

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