WO2010054524A1 - 一种非接触固定式荧光分子断层成像方法及装置 - Google Patents

一种非接触固定式荧光分子断层成像方法及装置 Download PDF

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WO2010054524A1
WO2010054524A1 PCT/CN2009/000518 CN2009000518W WO2010054524A1 WO 2010054524 A1 WO2010054524 A1 WO 2010054524A1 CN 2009000518 W CN2009000518 W CN 2009000518W WO 2010054524 A1 WO2010054524 A1 WO 2010054524A1
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light
optical
molecular tomography
disposed
contact fixed
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PCT/CN2009/000518
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English (en)
French (fr)
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白净
陈延平
董志华
汪待发
陈欣潇
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清华大学
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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
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • G01N21/6456—Spatial resolved fluorescence measurements; Imaging
    • 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 invention relates to a fluorescent molecular imaging method and device, in particular to a non-contact fixed fluorescent molecular tomography method and device. current technology
  • Fluorescence molecular tomography also known as glory molecular tomography or fluorescence diffusion tomography
  • Fluorescence molecular tomography using specific fluorescent molecules that have been used extensively in biological and medical research as probes Labeling specific molecules or cells, which perform in vivo observations of changes in the molecular level of the organism, and provide information such as the distribution of targets through image reconstruction, thereby overcoming the limitations of planar imaging, and thus obtaining more biological and medical behaviors. Information.
  • Fluorescence molecular tomography has the advantages of high sensitivity, quickness and simplicity, low cost, and relatively high flux. It not only supports the molecular events related to in vivo research, but also meets the requirements of systematically observing life processes in the 21st century. Rapid non-contact fluorescence molecular tomography can increase the survival rate of experimental animals, and is conducive to the construction of experimental animal models for a long period of time, thus improving the reliability of experimental animal models, and therefore has important practical significance for life science research.
  • the experimental animal body 111 is placed on the rotating table 112, the laser light emitted from the excitation light source 113 is scanned on the cross section of the experimental animal body 111, and the CCD camera 114 is placed on the other side of the experimental animal body 111, directly The experimental animal body 111 is photographed, and a series of high spatial resolution images of the fluorescence signal intensity information on the boundary of the experimental animal body 111 are obtained non-contactly.
  • a fluorescent filter 115 is disposed in front of the camera 114 for filtering out the excitation light. Only the fluorescence passes through the camera 114.
  • the excitation source-detector data pair can reach 10 6 , but because of the influence of factors such as the field of view, depth of field, exposure time and scattering characteristics of the biological tissue used in the method, Only the fluorescence signal image in a small local area on the boundary of the small animal body can be obtained, and the excitation light source-detector data pair available in the obtained fluorescence signal image is small, and the data set is less effective and the effective data set is small.
  • Luo Qingming et al. proposed a non-contact rotary diffusion fluorescence tomography system (application number: 200710053739.9, 200720087917.5), in which the experimental animal body 111 is fixed on a fixed clip, and the stepping motor drives the CCD camera 114 and the semiconductor laser to surround The experimental animals were rotated to obtain a 360° full-angle fluorescence signal at the boundary of the experimental animal.
  • this system has the same drawbacks, and it takes too long to acquire a series of fluorescent images.
  • the CCD camera 114 and the excitation light source 113 must be rotated relative to the experimental animal body 111 to obtain a 360° full-angle fluorescence signal on the boundary of the experimental animal body 111. If the imaging time of the system is long, It not only affects the survival of experimental animal body 111, but also is not conducive to the construction of small animal models in the body length, and the experimental imaging efficiency is low, it is difficult to achieve high-throughput experiments, which limits the application of fluorescence molecular tomography. Summary of the invention
  • an object of the present invention is to provide a non-contact fixed fluorescent molecular tomography method and apparatus which have a fast imaging speed and high image quality.
  • a non-contact fixed fluorescent molecular tomography method characterized in that: an excitation light source, a light switching component, a plurality of light transmission fibers, a plurality of optical lenses, and a transmission are provided.
  • An imaging device such as an optical fiber and a detector, wherein a plurality of optical transmission fibers and a plurality of optical lenses are respectively disposed around the object to be measured; and the optical switching component is controlled by a computer, and the excitation light emitted from the excitation light source is irradiated through any of the optical transmission fibers.
  • the fluorescence excited by the object to be measured is imaged at each fork end of the image fiber through each optical lens, and then transmitted to the detection end of the image fiber by the composite end of the image fiber. And sequentially switching the excitation light to the light-transmitting fiber at different positions through the optical switching component, repeating the above-mentioned fluorescence signal acquisition process, and obtaining the measured object at a full angle 360° fluorescence signal on the body boundary.
  • a fluorescent filter is disposed at the front end of the detector.
  • a fluorescent filter is disposed at a front end of each of the optical lenses.
  • An excitation light filter is disposed at a front end of the light switching member.
  • the device for implementing the above method comprises a plurality of light transmission fibers disposed around the object to be measured and a plurality of optical lenses, wherein the imaging planes of the optical lenses are respectively provided with a bifurcated end of the image fiber, the image fiber A detector is disposed at the light exit of the composite end; the other end of each of the light transmitting fibers is connected to a light switching component, and an excitation light source is disposed on the light incident side of the light switching component.
  • a fluorescent filter is disposed at a front end of the detector
  • a fluorescent filter is disposed at a front end of each of the lenses.
  • the excitation source is a semiconductor laser having a wavelength of 671 nm and an output of 200 mW.
  • An excitation light filter is disposed at a front end of the optical switching component.
  • the excitation source is a 150 watt tungsten halogen lamp.
  • the invention adopts the above technical solutions, and has the following advantages: 1.
  • the method of the invention is to fix the light-transmitting fiber and the lens around the object to be measured, and control the light switching component by computer to sequentially switch the excitation light to be set at different angles.
  • the light-transmitting fiber emits fluorescence by illuminating the object to be measured, so that both the object to be measured and the fluorescent imaging device are fixed and non-contact, and the system is stable in operation compared with the prior art, and can be widely used. Non-contact and fixed excitation of the luminescence of the fluorescent substance in the object to be measured, obtaining more stable fluorescent signals. 2.
  • the invention controls the optical switching component by computer, it is possible to extract more effective excitation light source-detector data pairs by increasing the number of light transmitting fibers and imaging optical fibers, and construct a larger excitation light source-detector data. Set, improve the quality of reconstructed images.
  • the method of the invention is to switch the excitation light emitted by the excitation light source into the corresponding light transmission fiber through the optical switching component, and is guided by the light transmission fiber to different positions, so that the excitation light incident point can be quickly switched by the computer, and the imaging is improved. speed. 4.
  • each of the optical lenses since a plurality of optical lenses are disposed around the object to be measured, each of the optical lenses only captures a part of the object, so that the shooting distance can be shortened, and the aperture of the optical lens can be maximized to make more objects to be measured.
  • the fluorescent signal enters the detector through the optical lens, which shortens the exposure time and further increases the imaging speed.
  • the invention can accurately collect the fluorescence signal of the object to be measured 360° at a full angle and non-contact, and has high imaging efficiency and high quality.
  • 1 is a schematic view showing the composition of an excitation light source, a light switching member, and a light transmission fiber in the present invention.
  • 2 is a schematic view showing the composition of an optical lens, an imaging fiber, and a detector in the present invention.
  • FIG. 3 is a schematic structural view of a transmission optical fiber in the present invention
  • FIG. 4 is a schematic view of the fluorescent filter of the present invention at the front end of the optical lens
  • FIG. 5 is a schematic view showing the excitation filter of the present invention between the excitation light source and the light switching member.
  • FIG. 6 is a schematic view showing the fluorescence filter of the present invention at the front end of the detector.
  • FIG. 7 is a schematic structural view of a fluorescent molecular imaging device in the prior art.
  • the method of the present invention is to provide an imaging device including an excitation light source 1, a light switching component 2, a plurality of light transmission fibers 3, a plurality of optical lenses 4, an imaging fiber 5, and a detector 6.
  • a plurality of light transmitting fibers 3 and a plurality of optical lenses 4 are disposed around the object 7 to be measured, respectively.
  • the light switching unit 2 is controlled by a computer (not shown), and the excitation light from the excitation light source 1 is irradiated onto the object 7 to be measured through any of the light transmission fibers 5, and the object 7 to be inspected is excited by each of the optical lenses 4.
  • the fluorescent images are imaged at the respective bifurcated ends 8 of the imaging fiber 5, and then transmitted through the composite end 9 of the imaging fiber 5 to the detector 6 disposed at the light exit of the imaging fiber 5, which is sequentially excited by the optical switching unit 2.
  • the light is switched to the light-transmitting fiber 3 at different positions, and the above-mentioned fluorescence signal acquisition process is repeated to obtain a full-angle 360° fluorescence signal on the boundary of the object 7 to be measured.
  • the method of the present invention is further described below by way of specific examples.
  • the apparatus of this embodiment includes a plurality of optical transmission fibers 31 to 324 and four optical lenses 41 to 44 disposed around the object 7 to be measured, and optical lenses 41 to 44 in each of the optical lenses 41 to 44.
  • a diverging end of the imaging fiber 5 is disposed at the imaging plane, and a detector 6 is disposed at the light exit of the composite end of the optical fiber 51-54; the other end of each of the optical fibers 31-324 is connected to an optical switching component 2,
  • the optical switching unit 2 is simultaneously connected to a computer for receiving an instruction from the computer to switch the excitation light to any of the light transmitting fibers 31 to 324.
  • An excitation light source 1 is disposed on the light-incident side of the light-switching member 2, and an excitation light filter 10 is disposed at the front end of the light-switching member 2, so that the excitation light capable of exciting the light-emitting band of the fluorescent substance in the object to be measured 7 is switched into the light. Part 2, while filtering out other stray light.
  • a fluorescent filter 11 is disposed at the front end of each of the optical lenses 41 to 44 to filter out interference such as excitation light, and only fluorescence is introduced into the optical lenses 41 to 44.
  • the excitation light source 1 can adopt a 150 watt tungsten halogen lamp source
  • the switching component 2 can adopt an off-the-shelf switcher
  • the light transmission fibers 31 to 324 can be selected from glass fiber or quartz fiber.
  • the optical lenses 41 to 44 employ lenses of four apertures ⁇ .0, and the optical lens illuminating surface faces the object 7 to be measured.
  • the other ends of the imaging fibers 51 to 54 are bundled into a composite terminal 13 (as shown in Fig. 4).
  • the detector 6 is a camera, and the camera can be a digital camera or other imaging device.
  • the excitation light from the excitation light source 1 is filtered by the excitation filter 10, reaches the optical switching component 2, and the optical switching component 2 is controlled by the computer, and the excitation light is passed through any of the optical transmission fibers 31 to 324.
  • the object 7 is irradiated onto the object 7 to be measured, and the fluorescence excited by the object 7 is passed through the fluorescent filter 11 through the optical lenses 41 to 44, and then imaged at the respective fork ends 81 to 84 of the image fiber, and then passed through the image.
  • the composite end 9 of the optical fiber is transmitted to the detector 6 disposed at the light exit of the imaging fibers 51 to 54, and the excitation light is sequentially switched to the light transmission fibers 31 to 324 at different positions by the optical switching unit 2, and the above-mentioned fluorescence signal acquisition is repeated.
  • the process achieves a 360° fluorescence signal on the boundary of the object 7 to be measured at full angle.
  • the device of this embodiment is mostly the same as that of Embodiment 1, but the excitation light source 1 in this embodiment uses a semiconductor laser having a wavelength of 671 nm and an output power of 200 mW, and thus the optical switching component 2
  • the excitation light filter 10 is not provided at the front end.
  • the number of light transmitting fibers 3 in this embodiment is 12, and more or less may be used.
  • each of the fluorescent filters 11 provided at the leading ends of the optical lenses 41 to 44 may be omitted, and only one fluorescent filter 11 may be disposed at the front end of the detector 6.
  • the optical switching unit 2 is first controlled by a computer, and the excitation light from the excitation light source 1 is irradiated onto the object 7 to be measured through any of the light transmission fibers 31 to 312, and is passed through the optical lenses 41 to 44.
  • the fluorescence excited by the measuring object 7 is imaged at each of the bifurcated ends 81 to 84 of the imaging fiber, and then filtered by the fluorescent end filter 11 through the composite end 9 of the imaging fiber, and then transmitted to the imaging optical fiber 51.
  • the computer sequentially switches the excitation light to the light-transmitting fibers 31 to 312 at different positions through the optical switching unit 2, and repeats the above-mentioned fluorescence signal acquisition process to obtain a 360° fluorescence signal at the boundary of the object 7 to be measured at a full angle.
  • the excitation filter 10 and the fluorescent filter 11 are each selected to have different filters depending on the excitation wavelength of the fluorescent substance in the object to be measured.
  • the optical lens 4 has the same number of bifurcated ends 8 as the imaging fiber 5, but the number can be selected as needed.
  • the structure, the installation position, and the connection of the components may be varied.
  • the improvement and equivalent transformation of the individual components shall not be excluded from the present invention. Outside the scope of protection.

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Description

一种非接触固定式荧光分子断层成像方法及装置 技术领域
本发明涉及一种荧光分子成像方法及装置， 特别是关于一种非接触固定式 荧光分子断层成像方法及装置。 现有技术
焚光分子断层成像 (Fluorescence molecular tomography, 亦称为荣光分子层 析成像或荧光扩散光层析成像） 利用已在生物学和医学研究中大量使用的具有 特异性的荧光分子作为探针， 用于标记特定分子或细胞， 其对生物体内分子水 平的变化进行在体观测， 并通过图像重建提供目标的分布等信息， 从而克服了 平面成像的局限性， 进而获得了更多有关生物学、 医学行为的信息。 荧光分子 断层成像具有灵敏度较高、 快捷简便、 费用低、 通量相对高等优点， 其不仅支 持在体研究有关的分子事件， 而且满足二十一世纪系统化地观测生命过程的要 求。 快速的非接触式荧光分子断层成像可增加实验动物的存活率， 有利于构建 长时间段的实验动物模型， 从而提高了实验动物模型的可靠性， 因此对于生命 科学研究具有重要的现实意义。
美国哈佛大学分子影像研究中心对稳态荧光分子断层成像的研究工作具有 代表性，该组提出的早期形式一一光纤接触式的荧光分子断层成像装置 (RALPH WEISSLEDER 等， Shedding light onto live molecular targets， 《 NATURE MEDICINE)), 2003： 123-128), 该装置采用成像腔， 实验时将动物浸泡在匹配 液中， 传光光纤接触成像腔。 该成像方法获取的激发光源-探测器数据集较小， 激发光源探测器数据对仅为 102-103对， 导致了重建图像的质量较差。 其后， 摒 弃了接触式光纤的耦合， 建立了非接触式荧光分子断层成像装置 （Nikolaos Deliolanis 等， Free-space fluorescence molecular tomography utilizing 360° geometry projections ， 《OPTICS LETTERS》， 2007:382-384)。 如图 7所示， 将 实验动物体 111置于旋转台 112上，激发光源 113发出的激光在实验动物体 111 横断面上进行扫描， 在实验动物体 111的另一侧放置 CCD相机 114， 直接拍摄 实验动物体 111，非接触地获得实验动物体 111的边界上荧光信号强度信息的一 系列高空间分辨率的图像。在相机 114前有一荧光滤光片 115，用于滤除激发光， 只让荧光通过进入相机 114。 虽然此方法获得较大数据集， 激发光源-探测器数 据对可达到 106， 但是因该方法所采用的相机的视场、 景深、 曝光时间与生物组 织的散射特性等因素的影响， 每次只能获取小动物体边界上局部较小范围内的 荧光信号图像， 所获得荧光信号图像中可用的激发光源 -探测器数据对少， 并且 数据集的有效性较差，有效数据集较小。为了全角度获取实验动物体边界上 360 °荧光信号的、 有效的大数据集， 以提高重建图像的质量， 须进行旋转实验动物 111， 小间隔（每隔 N度成像一次）地曝光成像， 但该种方法会导致成像次数 M (M=360/N) 多， 从而获取系列荧光图像需要的时间长。
骆清铭等提出了一种非接触旋转式扩散荧光层析成像系统 （申请号： 200710053739.9, 200720087917.5 ), 在该系统中实验动物体 111 固定于固定夹 上， 步进电机带动 CCD相机 114和半导体激光器围绕实验动物旋转， 以获得实 验动物体边界上 360°全角度的荧光信号。 与上述旋转小动物方式的荧光分子断 层成像系统一样， 该系统存在同样的不足之处， 也是获取系列荧光图像需要的 时间过长。
在现有的非接触式荧光分子断层成像中， CCD相机 114与激发光源 113必 须和实验动物体 111相对旋转， 以获得实验动物体 111边界上 360°全角度荧光 信号， 如果系统成像时间长， 不但影响了实验动物体 111 的存活， 不利于构建 在体长时段的小动物模型， 而且实验成像效率低， 难以实现高通量实验， 限制 了荧光分子断层成像的应用。 发明内容
针对上述问题， 本发明的目的是提供一种成像速度快、 成像质量高的非接 触固定式荧光分子断层成像方法及装置。
为实现上述目的， 本发明采取以下技术方案： 一种非接触固定式荧光分子 断层成像 法， 其特征在于： 设置一包括激发光源、 光切换部件、 多根传光光 纤、 多个光学镜头、 传像光纤和探测器的成像装置， 将多根传光光纤和多个光 学镜头分别设置在被测物体的周围； 通过计算机控制光切换部件， 将激发光源 发出的激发光通过任一传光光纤照射到被测物体上， 并通过各光学镜头将被测 物体激发出的荧光成像在传像光纤的各分叉端， 然后通过传像光纤的复合端传 输给设置在传像光纤出光口处的探测器， 依次通过光切换部件将激发光切换至 不同位置的传光光纤， 重复上述的荧光信号获取过程， 实现全角度获取被测物 体边界上 360°荧光信号。
在所述探测器的前端设置有一荧光滤光片。
在各所述光学镜头的前端设置一荧光滤光片。
在所述光切换部件的前端设置有一激发光滤光片。
实现上述方法的装置包括设置在被测物体的周围的多根传光光纤和多个光 学镜头， 各所述光学镜头的成像平面处分别设置有一传像光纤的分叉端， 所述 传像光纤复合端的出光口处设置有一探测器； 各所述传光光纤的另一端共同连 接一个光切换部件， 所述光切换部件的进光侧设置有一激发光源。
所述探测器的前端设置有一荧光滤光片
各所述镜头的前端设置一荧光滤光片。
所述激发光源为一波长为 671纳米、输出功率为 200毫瓦的半导体激光器。 所述光切换部件的前端设置有一激发光滤光片。
所述激发光源为一 150瓦的卤钨灯。
本发明由于采取以上技术方案， 其具有以下优点： 1、 本发明方法是将传光 光纤和镜头间隔固定在被测物体周围， 通过计算机控制光切换部件， 将激发光 依次切换到设置在不同角度的传光光纤上， 以照射被测物体激发产生荧光， 因 此无论是被测物体， 还是荧光成像设备都是固定非接触式设置的， 与现有技术 相比， 系统运行稳定， 可以大范围、 非接触并固定式地激发被测物体内荧光物 质的发光， 获取更多稳定的荧光信号。 2、 本发明由于是通过计算机控制光切换 部件， 因此可以通过增加传光光纤和传像光纤的数量， 提取更多有效的激发光 源一探测器数据对， 构建更大的激发光源一探测器数据集， 提高重建图像的质 量。 3、 本发明方法是将激发光源发出的激发光经光切换部件切换入相应的传光 光纤， 由传光光纤导引至不同位置， 因此可以通过计算机实现快速切换激发光 入射点，提高了成像速度。 4、本发明由于在被测物体周围设置了多部光学镜头， 每一个光学镜头仅拍摄物体的一部分， 因此可以缩短拍摄距离， 将光学镜头的 光圈幵到最大， 使更多的被测物体的荧光信号通过光学镜头进入探测器， 从而 缩短了曝光时间， 进一步提高了成像速度。 本发明能够 360°全角度、 非接触固 定地釆集被测物体的荧光信号， 并且成像效率、 质量高。 附图说明
图 1 是本发明中激发光源、 光切换部件和传光光纤的组成示意图 图 2 是本发明中光学镜头、 传像光纤和探测器的组成示意图
图 3 是本发明中传像光纤的结构示意图
图 4 是本发明荧光滤光片位于光学镜头前端的示意图
图 5 是本发明激发滤光片位于激发光源和光切换部件之间的示意图 图 6 是本发明荧光滤光片位于探测器前端的示意图
图 7 是现有技术中荧光分子成像装置的结构示意图 本发明最佳实施方式
下面结合附图和实施例对本发明进行详细的描述。
如图 1〜图 3所示， 本发明方法是设置一包括激发光源 1、 光切换部件 2、 多根传光光纤 3、 多个光学镜头 4、 传像光纤 5和探测器 6的成像装置， 将多根 传光光纤 3和多个光学镜头 4分别设置在被测物体 7的周围。 首先通过计算机 (图中未示）控制光切换部件 2，将来自激发光源 1的激发光通过任一传光光纤 5照射到被测物体 7上，并通过各光学镜头 4将被测物体 7激发出的荧光成像在 传像光纤 5的各分叉端 8，然后通过传像光纤 5的复合端 9传输给设置在传像光 纤 5出光口处的探测器 6，依次通过光切换部件 2将激发光切换至不同位置的传 光光纤 3， 重复上述的荧光信号获取过程， 实现全角度获取被测物体 7边界上 360°荧光信号。 下面通过具体实施例对本发明方法进行进一步描述。
实施例 1 :
如图 4、 图 5所示， 本实施例的装置包括一设置在被测物体 7的周围的 24 根传光光纤 31〜324和 4个光学镜头 41〜44，在各光学镜头 41〜44的成像平面 处分别设置有一传像光纤 5的分叉端，传像光纤 51〜54复合端的出光口处设置 有一探测器 6; 各传光光纤 31〜324的另一端共同连接一个光切换部件 2， 光切 换部件 2 同时连接一计算机， 用于接收计算机的指令， 以将激发光切换到任一 传光光纤 31〜324。 在光切换部件 2的进光侧设置有一激发光源 1， 在光切换部 件 2的前端设置有一激发光滤光片 10， 这样使能够激发被测物体 7内荧光物质 发光波段的激发光进入光切换部件 2，而滤除其它杂光。同时在各光学镜头 41〜 44的前端分别设置了一个荧光滤光片 11， 用于滤除激发光等干扰， 仅使荧光进 入光学镜头 41〜44内。
上述实施例中， 激发光源 1可以采用一 150瓦的鹵钨灯光源， 切换部件 2 可以采用一现成的切换器， 传光光纤 31〜324可以选用玻璃光纤或石英光纤。 光学镜头 41〜44采用四个光圈 Ω.0的镜头，且光学镜头采光面朝向被测物体 7。 传像光纤 51〜54的另一端集束成一复合端 13 (如图 4所示）。 探测器 6是一个 相机， 相机可以是数码相机， 也可以是其它成像装置。
本实施例使用时， 首先来自激发光源 1的激发光经激发滤光片 10滤光后， 到达光切换部件 2， 通过计算机控制光切换部件 2, 将激发光通过任一传光光纤 31〜324照射到被测物体 7上， 通过各光学镜头 41〜44将被测物体 7激发出的 荧光经过荧光滤光片 11后，成像在传像光纤的各分叉端 81〜84，然后通过传像 光纤的复合端 9传输给设置在传像光纤 51〜54出光口处的探测器 6， 依次通过 光切换部件 2将激发光切换至不同位置的传光光纤 31〜324，重复上述的荧光信 号获取过程， 实现全角度获取被测物体 7边界上 360°荧光信号。
实施例 2:
如图 6所示， 本实施例的装置大部分与实施例 1相同， 但是本实施例中的 激发光源 1采用一波长 671纳米、 输出功率 200毫瓦的半导体激光器， 因此在 光切换部件 2的前端不用设置激发光滤光片 10。本实施例中的传光光纤 3为 12 根， 也可以更多或更少。 另外设置在光学镜头 41〜44前端的各荧光滤光片 11 也可以不设置， 而仅将一个荧光滤光片 11设置在探测器 6前端。
本实施例使用时， 首先通过计算机控制光切换部件 2， 将来自激发光源 1 的激发光通过任一传光光纤 31〜312照射到被测物体 7上， 并通过各光学镜头 41〜44将被测物体 7激发出的荧光成像在传像光纤的各分叉端 81〜84，然后通 过传像光纤的复合端 9经过荧光滤光片 11滤除激发光后， 传输给设置在传像光 纤 51〜54出光口处的探测器 6。 计算机通过光切换部件 2依次将激发光切换至 不同位置的传光光纤 31〜312，重复上述的荧光信号获取过程， 实现全角度获取 被测物体 7边界上 360°荧光信号。
上述各实施例中， 激发滤光片 10和荧光滤光片 11均是根据被测物体 Ί内 的荧光物质的激发波长不同， 来选择不同的滤光片。 光学镜头 4与传像光纤 5 上的分叉端 8的数目相同， 但该数目可以根据需要进行选择。
上述各实施例中， 各部件的结构、 设置位置、 及其连接都是可以有所变化 的， 在本发明技术方案的基础上， 对个别部件进行的改进和等同变换， 不应排 除在本发明的保护范围之外。

Claims

权利要求
1、 一种非接触固定式荧光分子断层成像方法， 其特征在于： 设置一包括激 发光源、 光切换部件、 多根传光光纤、 多个光学镜头、 传像光纤和探测器的成 像装置， 将多根传光光纤和多个光学镜头分别设置在被测物体的周围； 通过计 算机控制光切换部件， 将激发光源发出的激发光通过任一传光光纤照射到被测 物体上， 并通过各光学镜头将被测物体激发出的荧光成像在传像光纤的各分叉 端， 然后通过传像光纤的复合端传输给设置在传像光纤出光口处的探测器， 依 次通过光切换部件将激发光切换至不同位置的传光光纤， 重复上述的荧光信号 获取过程， 实现全角度获取被测物体边界上 360°荧光信号。
2、 如权利要求 1所述的一种非接触固定式荧光分子断层成像方法， 其特征 在于： 在所述探测器的前端设置有一荧光滤光片。
3、 如权利要求 1所述的一种非接触固定式荧光分子断层成像方法， 其特征 在于： 在各所述光学镜头的前端设置一荧光滤光片。
4、如权利要求 1或 2或 3所述的一种非接触固定式荧光分子断层成像方法， 其特征在于： 在所述光切换部件的前端设置有一激发光滤光片。
5、如权利要求 1或 2或 3所述的一种非接触固定式荧光分子断层成像方法， 其特征在于： 所述光学镜头在拍摄时采用最大光圈。
6、 如权利要求 4所述的一种非接触固定式荧光分子断层成像方法， 其特征 在于： 所述光学镜头在拍摄时采用最大光圈。
7、 一种实现如权利要求 1〜6所述方法的非接触固定式荧光分子断层成像 装置， 其特征在于： 它包括设置在被测物体的周围的多根传光光纤和多个光学 镜头， 各所述光学镜头的成像平面处分别设置有一传像光纤的分叉端， 所述传 像光纤复合端的出光口处设置有一探测器； 各所述传光光纤的另一端共同连接 一个光切换部件， 所述光切换部件的进光侧设置有一激发光源。
8、 如权利要求 7所述的一种非接触固定式荧光分子断层成像装置， 其特征 在于： 所述探测器的前端设置有一荧光滤光片
9、 如权利要求 7所述的一种非接触固定式荧光分子断层成像装置， 其特征 在于： 各所述镜头的前端设置一荧光滤光片。
10、 如权利要求 7或 8或 9所述的一种非接触固定式荧光分子断层成像装 置， 其特征在于： 所述激发光源为一波长为 671纳米、 输出功率为 200毫瓦的 半导体激光器。
11、 如权利要求 7或 8或 9所述的一种非接触固定式荧光分子断层成像装 置， 其特征在于： 所述光切换部 #的前端设置有一激发光滤光片。
12、 如权利要求 11所述的一种非接触固定式荧光分子断层成像装置， 其特 征在于： 所述激发光源为一 150瓦的卤钨灯。
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