JP4983929B2 - Biological image acquisition device - Google Patents

Description

  The present invention relates to an optical bioimaging technique for a biological sample such as a small animal. In particular, the present invention relates to a technique for avoiding image degradation caused by a backlight problem of illumination in an apparatus that simultaneously captures multidirectional images of a living body.

  The technique of imaging how molecular species in a living body are distributed is an important research method in medicine and biology. At the cellular level, methods for imaging molecular species using a microscope with a molecular probe attached with a fluorescent dye or a molecular probe using chemiluminescence have been widely used. In the future, there will be a demand for an apparatus for observing the distribution of the molecular species of interest from the cellular level to larger organs and even individual animals. For example, it is a technique in which a fluorescent probe binds to a cancer cell in an individual such as a mouse to image the state of growth of the cancer cell of interest and observe it as a time-dependent change such as daily or weekly. In order to observe the growth of cancer cells inside an animal individual with a conventional measuring device for cell level, the animal is killed and a predetermined part is stained or a fluorescent substance is attached, but then, It is not possible to see the growth of cells over time for a single individual. For this reason, it is desired to develop a device that can observe the molecular species of the internal information of a small animal individual while the individual is alive.

  Near-infrared light has a relatively good light transmittance inside the living body, and therefore, a small animal observation apparatus using a wavelength of about 600 nm to 900 nm is used. However, in the conventional observation method, usually, a sample is photographed from the upper side, and simultaneous observation in multiple directions is not possible. For example, when a mouse is observed from a specific direction, cancer is detected when observed from the opposite side even if the cancer is not visible. When using a device that can observe only one direction, the operator is forced to take an image that is rotated little by little around the body axis of the mouse, so that it can be handled by an operation that approximates multi-directional observation. There is only. However, with this method, reproducible data cannot be obtained, and each direction cannot be detected simultaneously. In particular, since the emission intensity itself is very weak in luminescence observation from a living body, it is usually necessary to perform integral exposure on a two-dimensional detector for several tens of seconds to several minutes. On the other hand, since the light emission intensity changes with time, it is not useful to sequentially switch images in different directions to change the image conditions for each direction. It is desirable that images in multiple directions of the living body can be integrated on the detector for a long time in parallel. Although fluorescence image measurement can be performed in a relatively short time, the ability to capture information in multiple directions at once is indispensable for obtaining quick and accurate data.

  As a method for obtaining multi-directional images, a method is known in which images of a large number of angles are sequentially acquired in a time-sharing manner using a rotating reflector (see Patent Document 1). This method does not rotate the sample nor the two-dimensional detector, but the multi-directional observation is performed by rotating the mirror in the middle and changing the position of the sample, although there is a parallel movement of the sample itself. . The disadvantage of the method of Patent Document 1 using a rotating mirror is that the measurement in each direction is time-division, so simultaneous measurement cannot be performed, time is required for the measurement, and the time is different for each direction. When the intensity changes with time, it is inaccurate and the structure is complicated.

  Several imaging optical systems that do not use a rotating reflector are known (see Patent Document 2-9). References 2 and 3 describe the concept of multi-directional observation and an imaging optical system including a reflecting mirror and a two-dimensional detector used therefor. However, the multi-directional observation apparatus is merely an apparatus targeted by the present invention. Not touching the backlight problem. The cited document 4 relates to a “method for utilizing” light from the opposite side of the camera, and has no common point with the present invention on the theme of “a method for avoiding” light from the opposite side of the camera. Since Cited Document 6 describes a method of photographing around 360 ° of the camera, not multi-directional observation around the sample, the sample and the camera are interchanged with the present invention, which is irrelevant to the present invention. is there. Cited references 5, 7, and 8 do not handle even multi-directional observation. Although the concentric arrangement of the light source happens to be seen in FIG. 1 of the cited document 7, it is not a hint of the present invention because it is different from the concept of arrangement as a method for solving the backlight problem. The following is a detailed examination of the above contents for each document.

  The cited document 2 describes an invention for the purpose of taking a stereoscopic image of a subject. The invention is common to the present invention only by using a polygon mirror, but it does not aim to obtain biological information such as a fluorescent image. In addition, there is a description that the angle of the reflecting mirror is changed to increase the observation direction, but this is a partial time division, which is a contradictory direction for the purpose of simultaneous measurement. Although there is a description that the light source is arranged, this light source simply illuminates the back side of the sample because it darkens, and it does not discuss the obstacle of the backlight problem due to the light source illuminating the back side, of course, directly to the camera As can be seen from the fact that no consideration is given to the possibility of incidence, it cannot be a hint of the theme of the present invention to solve the backlight problem associated with simultaneous measurement in multiple directions.

  Cited Document 3 proposes the use of a cylindrical convex mirror for expanding the imaging range of a video camera installed in a fruit transport line, and is common with the present invention in that an image taken by a reflecting mirror is photographed together with the object itself. However, it does not even describe the illumination light source, and cannot be a hint of the theme of solving the backlight problem associated with the multidirectional simultaneous measurement of the present invention.

  Cited Document 4 relates to an apparatus for inspecting a missing portion by leakage light from an inspection surface such as a printed wiring board, and discusses a method for detecting leakage light from a light source located on the other side of the printed board to be inspected. . Whereas the present invention discusses “a method of avoiding” the backlight coming from the opposite side of the camera, the invention of the cited document 4 is a “method of using” the light coming from the opposite side of the camera, from the opposite side. There is no common point with the present invention on the theme of “light avoiding technique”. Although light reflected from the missing part in several directions is received by a plurality of mirrors, it cannot be a hint of the present invention.

  Reference 5 relates to an apparatus for detecting a fluorescent image of a biological sample subjected to electrophoresis or the like with a CCD. When the size of the sample changes, it is necessary to move the sample closer to or away from the camera. At that time, a method for compensating for data fluctuation due to a difference in the distance of the fluorescence excitation light source is discussed. However, the fluorescence observation direction is only one direction, and the disadvantage of backlighting is not regarded as a problem at all. FIG. 2 of the cited document 5 only describes irradiation from two directions of the bottom light source 51 and the incident light limit 52 as the light source. Therefore, even if the fluorescent device is described, there is no description that can be a hint of the present invention.

  Cited Document 6 deals with an invention related to a panoramic camera, that is, a technique for photographing a 360 degree direction around the camera. On the other hand, since the multi-directional measurement of the present invention is a device that takes a sample image from a plurality of directions around the sample (measurement target), the positional relationship between the camera and the sample is opposite. It is obvious that the cited document 6 is irrelevant to the present invention. Occasionally, we are only using a polyhedral mirror to capture the 360 ° direction around the camera. Of course, it is not related to the backlight problem of the present invention.

  Cited Document 7 relates to a technique used for a surveillance camera, which is an apparatus for simultaneously irradiating a subject with irradiation light from three or more directions and imaging from one direction. By changing the frequency (wavelength) of the irradiation light according to the irradiation direction, and simultaneously selecting the filter for each pixel of the detector in the camera according to the frequency (wavelength) according to the irradiation direction It is an invention in which images for each irradiation direction are acquired while multi-directional irradiation is performed, and images in various irradiation directions are obtained by weight calculation. There is some relevance to the present invention in terms of multi-directional “illumination”. However, although the present invention deals with the problems associated with multi-directional imaging, the cited document 7 is imaging from one direction and does not deal with the backlight problem at all. Although there is a diagram with a backlight arrangement in FIG. 1, there is no description that recognizes it as inconvenient, so even one observation direction is not an example of handling backlight. It cannot be said that there is a description that gives hints for solving the backlight problem associated with direction observation.

  Cited Document 8 describes an invention related to an endoscope. Among them, imaging with irradiation light with different wavelengths and devices that capture fluorescent images are described, so there is naturally a description of fluorescent light sources, but there is no description of multi-directional observation, and the back light of the excitation light Since the problem is not described, it is impossible to give a hint for solving the backlight problem associated with the multi-directional observation which is the object of the present invention.

  Patent Document 9 discloses backside illumination at the time of fluorescence measurement. In this case, a fluorescence excitation light source is disposed in contact with the back surface of the biological sample so that the light source cannot be seen from the camera side. That is, the light source is hidden by the sample itself. Although this method enables backside illumination by a unidirectional observation method, it is clearly a method that cannot be used for multidirectional observation, and if the sample is removed, strong light enters the detector. The present invention is completely different from that of Patent Document 9 in that it aims at a configuration in which light does not directly enter the detector regardless of the presence or absence of the sample.

US Patent Application Publication No. 20050201414 JP 2001-330915 A JP-A-10-124648 Japanese Patent Laid-Open No. 3-111745 JP 2003-287497 A JP-A-8-125835 International Publication No. 2007/108070 Pamphlet JP 2005-13611 A US Pat. No. 6,922,246

  An object of the present invention is to provide a device that avoids reflection of a light source and blurring of an image that cause a backlight problem during illumination, in the above-described biological image acquisition device capable of simultaneous observation in multiple directions.

  In general, there are two types of illumination for biometric image measurement, one is illumination for appearance image acquisition, and the other is illumination of fluorescence excitation light. The illumination for obtaining the appearance image is a function necessary for both the fluorescence image and the luminescence image because it is used when the appearance image is displayed on the fluorescence image or the luminescence image obtained separately. Of course, the illumination of the fluorescence excitation light is only relevant when photographing fluorescent images.

  In the multi-directional simultaneous photographing, there is a problem that the above-described two kinds of illuminations are backlit in any one of the imaging directions, and thus it is necessary to solve the disadvantages at that time. However, cited references 1-9 do not disclose the problem of backlighting during illumination.

  The biological image acquisition device of the present invention includes a sample table on which a biological sample is placed, a two-dimensional detector, light from the sample on the sample table toward the two-dimensional detector, and other directions. An imaging optical system that guides light to the two-dimensional detector and forms a plurality of guided images on the two-dimensional detector, and is disposed outside the range of the field of view of the two-dimensional detector through the imaging optical system. A light source device that irradiates light onto a sample on a sample stage and an image display device that displays an image captured by a two-dimensional detector are provided.

  “Light in the direction toward the two-dimensional detector” means light in a direction in which the two-dimensional detector can directly receive light.

  In the present invention, the light source device is arranged outside the range of the field of view of the two-dimensional detector through the imaging optical system. This is to avoid the backlight problem that occurs during illumination in multi-directional observation, that is, to prevent the two-dimensional detector from directly receiving strong illumination light from the light source. When the two-dimensional detector directly receives light from the light source, the direct light from the light source is very strong, so not only the corresponding pixel of the two-dimensional detector such as a CCD is saturated, but also excessive charges are adjacent. This causes so-called blooming, in which a large range of pixels in the vicinity of saturated pixels cannot be photographed. In particular, in the appearance image observation, the wavelength component of the light source is guided to the detector without being removed by a filter, so that blooming is likely to occur when direct light from the light source enters. On the other hand, in the fluorescence image observation, the wavelength component contained in the light source is removed by the filter before entering the detector, so the trouble when the direct light of the light source enters is leaked light due to insufficient filter rejection rate, usually leading to blooming. Not so good. Nevertheless, unnecessary light emission is reflected in a part of the measurement data, which is confused with the original fluorescence from the sample. Therefore, the present invention has been devised to avoid direct light reception regardless of appearance image observation or fluorescence image observation. Yes.

  As described above, according to the present invention, in the multidirectional biological image acquisition apparatus, the reflection of the light source and the blurring of the image due to the backlight problem are avoided.

  In conventional imaging of images from one direction that is not multi-directional, the backlight problem did not occur with respect to the above-mentioned light source for external illumination or fluorescence excitation, but at least opposite the sample, such as from above and below the sample. Since it has been found that the multidirectional biological image acquisition apparatus that simultaneously captures the side image causes inconvenience due to the position of the irradiation light source, the present invention was born as a result of careful consideration of means for avoiding this.

  The avoidance means draws the direct and indirect field of view range of the camera as shown in FIGS. 3A and 3B, and the direct light from the light source is prevented from entering the CCD by removing the light source positions of the outline acquisition light source and the fluorescence excitation light source from the range. To do. Here, the indirect visual field range means a visual field range reflected on the two-dimensional detector through an optical system such as a reflecting mirror. Thus, even in an apparatus that simultaneously captures images on the opposite side of the sample, a living body image capturing apparatus that fully utilizes the advantages of multidirectional imaging can be constructed by avoiding that direct light of irradiated light enters the CCD.

  Here, as another method in which the direct light from the light source does not enter the CCD, a method of using “indirect illumination of the sample” instead of the light source directly illuminating the sample was examined. That is, it is a technique for avoiding the direct light of the photogen from reaching the CCD by shooting the image by applying the light diffusely reflected by the scattering plate or the wall to the sample. However, testing this proved inconvenient for the following reasons: That is, during indirect illumination, light that reaches the CCD after being reflected from the sample (light for measurement) is in the order of light source → diffuser plate → sample → CCD. However, if there is a diffuser plate in the direct or indirect field of view of the camera, light (interfering light) in the path of light source → diffuser plate → CCD exists. If the diffuse reflector is viewed as a light source, the direct light from the diffuse reflector will reach the CCD, which will be stronger than the light intended for measurement.

  To express the problem-solving points found in this way more accurately, it is said that the number of diffuse reflections that reach the CCD for the light reflected from the sample (light for measurement) is the same as or less than the number of diffuse reflections of interference light. It is a requirement to satisfy the conditions. In the example of FIG. 1, as for “light for measurement”, the light source directly irradiates the sample first, and the reflected light (or fluorescence) enters the CCD. On the other hand, in the case of disturbing light, even if a wall or the like is illuminated by a light source, the diffusely reflected light enters the CCD, and the number of reflections is equal to or less than “light for measurement”. If you want, here it is better not to illuminate the surrounding walls, but in practice it is impossible, so we will deal with it by making the surrounding walls of a material with as low a reflectance as possible and reducing the reflected light.

  In this manner, it was found that if the light scattered from other than the sample and reaching the detector is removed, there is no light reaching the wall near the sample, so that only the sample can be clearly lifted and photographed.

  To put it together again using the concept of the number of reflections, if the illumination light source is placed outside the direct and indirect field of view of the camera, the number of reflections of the `` light for measurement '' reflected by the sample will be `` jamming light '' such as walls. Less than or at least the same number of reflections. As a result, it is possible to avoid image degradation due to backlight and obstacles to light source reflection, and a clear sample image can be obtained.

Preferably there is only one two-dimensional detector.
When simultaneously obtaining observation images from multiple directions of sample light, a method of forming an image of multidirectional light on one two-dimensional detector and two or more two-dimensional detectors are combined. Although a method of imaging can be considered, the configuration can be simplified by reducing the cost by using one two-dimensional detector.

  A plurality of two-dimensional detectors may be provided. In that case, each two-dimensional detector is arranged at a position where the sample on the sample stage can directly receive light in different directions, and an imaging optical system is provided for each two-dimensional detector. preferable. By doing so, each two-dimensional detector can image light in two or more directions from each sample, as in the example in which two detectors each handle two directions and obtain a total of four directions. The cost can be reduced compared to the case where a two-dimensional detector is provided for each imaging direction.

  In a preferred embodiment of the light source device for disposing the light source outside the range of the field of view of the two-dimensional detector, the two-dimensional detector is disposed at a position for imaging from a direction perpendicular to the sample placement surface of the sample table, The light source device includes a light source holding unit that holds a plurality of light sources, and the light source holding unit holds a light source for obtaining an appearance image or a fluorescence excitation light source in a plane perpendicular to the body axis of the biological sample on the sample stage. The imaging optical system includes a mechanism that inserts a filter between the sample and the two-dimensional detector that shields the excitation light wavelength component and transmits only the fluorescence wavelength only during fluorescence imaging.

  As a more specific example, a light source holding unit may hold an excitation light source on a circumference centered on a point on a body axis extension line of a biological sample on a sample stage.

  The circumference may be composed of two or more concentric circumferences having different radii. In this way, an excitation light source that emits more types of wavelength light can be arranged without increasing the light source holding unit, and therefore, a light source that emits wavelength light corresponding to various different fluorescent dyes can be arranged to adjust the excitation wavelength. The range of selection can be expanded.

  In addition, the light source device rotates the light source holding unit, a support mechanism that supports the light source holding unit so that the light source holding unit can rotate around the circumference of the circumference holding the light source for appearance image acquisition or the fluorescence excitation light source. And a drive mechanism to be provided. By doing so, the biological sample can be irradiated from any position with the light source that emits the wavelength light according to the application by holding the light source holding unit with various kinds of light sources that emit the wavelength light corresponding to various different fluorescent dyes. become.

  The light source for appearance illumination included in the light source device captures the appearance image of the sample with a two-dimensional detector and displays the image by superimposing it on the light emission image or fluorescence image of the living body to emit light or emit fluorescence. Necessary to associate with a place. The external illumination light source can be realized simply by intentionally removing the wavelength component of the illumination light during the appearance image measurement, so it is possible to provide a dedicated light source for external illumination, or use a fluorescent illumination light source for external illumination. It can also be used as a light source.

  An example of the imaging optical system includes a reflecting mirror that reflects light of an image of a part that cannot be directly imaged by the two-dimensional detector and guides the light to the two-dimensional detector. According to this configuration, by increasing the number of reflecting mirrors, the image of the sample viewed from more directions can be simultaneously captured by the two-dimensional detector.

  In addition, the imaging optical system preferably includes an auxiliary imaging lens that corrects the optical path length difference of light of a plurality of images formed on the two-dimensional detector.

  An exemplary embodiment of the present invention will be described with reference to FIG.

  The biological image acquisition apparatus shown in FIG. 1 is capable of simultaneously observing a biological sample 4 such as a small animal (typically a mouse) placed on a transparent sample stage 2 from above and below, An image viewed from above and below the biological sample 4 is formed on a common two-dimensional detector (CCD camera) 6 via a common main imaging lens 8 disposed at the top.

  The image on the back side is reflected by the two reflecting mirrors M1 and M2 and guided to the same two-dimensional detector 6, and the front (0 °) and back side (180 °) of the biological sample 4 as shown in FIG. ) Is simultaneously displayed on the two-dimensional detector 6. Since the image on the back side is slightly smaller than the image on the front side because it is far away from the image on the front side, it can be displayed with the enlargement factor corrected finally. Further, since the distance (optical path length) differs depending on the reflecting mirror, blur occurs on the two-dimensional detector 6, but blur can be eliminated by inserting the auxiliary concave lens 12 and adjusting the focal point.

  By the way, such a biological image acquisition apparatus is provided with an illumination for appearance image of the biological sample 4 and a light source device for irradiation with fluorescence excitation light. As described above, images of the biological sample 4 from multiple directions can be obtained. When acquiring, the light source of a light source device may be arrange | positioned on the opposite side to the two-dimensional detector 6 on both sides of the biological sample 4, and may be reflected in the two-dimensional detector 6. FIG. For example, when imaging the back surface of the biological sample 4, a light source is disposed below the biological sample 4 and light is irradiated toward the back surface of the biological sample 4. In such a state, direct light from the light source is incident on the two-dimensional detector 6 to cause problems such as blooming. Even when the light source is arranged on the same side as the two-dimensional detector 6 and illuminated, the light from the light source may be reflected by the multi-directional observation reflecting mirror and enter the CCD camera. Direct light enters the two-dimensional detector 6 through the reflecting mirror. Conventionally, since a biological sample is observed only from a single direction, such a problem does not occur because the light source is not disposed opposite to the camera and there is no reflecting mirror.

  In order to solve the above problem, in the example of FIG. 1, the light source units S1 to S4 and S1 ′ to S4 ′ of the light source device that irradiates light from multiple directions are directly viewed through the reflecting mirror of the two-dimensional detector 6. And it arrange | positions so that it may not enter into the indirect visual field through a reflective mirror. The arrangement method is shown more specifically in FIGS. 3A and 3B.

  3A and 3B show an example of a biological image acquisition device that can observe a biological sample from three directions (0 ° in front, 144 ° 212 °), and FIG. 3A shows an animal 4 that is a biological sample. FIG. 3B is a diagram viewed from the side of the body axis, and FIG.

  The lens 8 and the two-dimensional detector 6 are arranged directly above the animal 4, and the two reflectors M <b> 1 are obliquely below the animal so that an image in the direction of 144 ° 212 ° is formed on the same two-dimensional detector 6. , M2 are arranged so that observation from a total of three directions including 0 ° in the front can be performed.

  The light source device that performs light irradiation from multiple directions toward the biological sample 4 holds the light source units S1 to S4 at equal intervals on a circumference centered on a point on the body axis extension line on the head side of the biological sample 4. The light source holding part 14a and the light source holding part 14b which hold | maintain light source part S1'-S4 'at equal intervals on the circumference centering on the point on the body-axis extension line of the tail part side of the biological sample 4 are provided.

  In order to prevent backlighting, it is a problem how to arrange these light source parts S1 to S4 and S1 'to S4'. The hatched portions 16 and 18 in FIGS. 3A and 3B indicate “the field of view of the two-dimensional detector 6 in multi-directional observation”. The triangular hatched portion 16 below the lens 8 is the direct field of view of the two-dimensional detector 6, which is the same as in the case of conventional one-way observation. In this example, reflecting mirrors M1 and M2 are added, so that an indirect field of view of the camera via the reflecting mirrors M1 and M2 exists, which is a hatched portion 18.

  When the light source unit is in the direct visual field range 16 or the indirect visual field range 18 indicated by hatching, direct light from the light source unit enters the two-dimensional detector 6 and causes inconveniences such as blooming. Therefore, as shown in FIG. 3A, the light source units S1 to S4 and S1 ′ to S4 ′ are positioned obliquely with respect to the biological sample 4 so as not to enter the direct visual field 16 and the indirect visual field 18 of the two-dimensional detector 6. By arranging and irradiating light obliquely, direct light from the light source parts S1 to S4 and S1 ′ to S4 ′ can be prevented from entering the two-dimensional detector 6.

  Furthermore, by arranging the light source parts S1 to S4, S1 'to S4' on a circumference centered on one point on the extension line of the body axis of the animal 4, the uniformity of irradiation can be improved. And by arranging the light source holders 14a and 14b so that the biological sample is sandwiched from the head side and the tail side of the biological sample 4, the uniformity of irradiation can be improved and the shadow in the biological sample 4 can be reduced. . Although the direct visual field and the indirect visual field corresponding to FIG. 1 are slightly different from those in FIG. 3, they can be considered in the same manner based on the principle explained in FIG.

  Next, referring back to FIG. 1, the light source units S1 to S4 and S1 ′ to S4 ′ of the light source device will be described. The light source units S1 to S4 and S1 'to S4' of the light source device include light sources A, B, and C, respectively.

  A light source A is an illumination light source for obtaining an appearance image of a sample such as a white light emitting diode (hereinafter referred to as a white LED), and the sample is obtained by photographing the four light sources A on the light source holding portion 14a in a lighting state. 4 appearance images of 0 ° and 180 ° can be obtained.

  The light sources B and C are fluorescence excitation light sources that generate excitation light having different wavelengths. The excitation light sources B and C irradiate the sample with light emitted from a light emitting element such as a laser diode through an interference filter. At the time of photographing, a fluorescent side filter 10 is inserted between the sample 4 and the photographing lens 8. The fluorescence side filter is selected so as to block all light having a wavelength that passes through the excitation filter. This prevents interference by the scattered light having the excitation wavelength, and forms fluorescent images of 0 ° and 180 ° on the CCD 6 through the lens 10 only with the fluorescent component converted from the excitation wavelength to the fluorescence wavelength. be able to.

In FIGS. 1 and 3, only the circumferential portions that hold the light source portions S1 to S4 and S1 ′ to S4 ′ are shown as the light source holding portions 14a and 14b.
Similarly, in the example of FIG. 3, four light sources A are turned on and appearance images of 0 °, 144 °, and 212 ° are turned on, and four light sources B or C are turned on and fluorescent images of 0 °, 144 °, and 212 ° are turned on. Can be obtained.

  The present invention provides a light source of a light source device necessary for acquiring an appearance image or a fluorescence image of a biological sample as a means for avoiding the backlight problem of illumination that occurs in a multi-directional observation apparatus of a living body through an imaging optical system of a two-dimensional detector. Since it is arranged outside the range of the field of view, it is possible to prevent image degradation due to direct light from the light source, blooming due to backlight, etc., and obtain a clear multidirectional biological image. In the multidirectional observation apparatus of the present invention, light in a plurality of different directions from the biological sample is simultaneously imaged on the two-dimensional detector by the imaging optical system. In addition, the above backlight problem can be avoided while easily and simultaneously observing images of fluorescence or appearance.

It is a schematic block diagram which shows one Example of a biometric image acquisition apparatus. It is a figure which shows an example of the captured image of the biometric image acquisition apparatus of the Example. It is the figure seen from the side of the biological sample of the biological image acquisition apparatus for demonstrating the positional relationship of the direct visual field and indirect visual field of a two-dimensional detector, and each light source device. It is the figure seen from the head side of the biological sample of the biological image acquisition apparatus for demonstrating the positional relationship of the direct visual field and indirect visual field of a two-dimensional detector, and each light source device. It is a perspective view which shows roughly an example of a structure of a light source part. It is a graph which shows an example of the relationship between the emission spectrum of an excitation light source, and the transmission spectrum of an interference filter and the fluorescence side filter. It is a schematic block diagram which shows the 2nd Example of a biometric image acquisition apparatus. It is a figure which shows an example of the captured image of the biometric image acquisition apparatus of the Example. It is the picked-up image image | photographed in the state in which the light source has entered into the direct visual field or indirect visual field of a two-dimensional detector. It is a figure which shows roughly another example of a structure of a light source device. It is a schematic block diagram which shows the Example of the biological image acquisition apparatus using a some two-dimensional detector. It is a schematic block diagram which shows the modification of a light source device. It is a schematic block diagram which shows the further modification of a light source device. It is a perspective view which shows the structure of the 3rd Example which uses a concave mirror. It is explanatory drawing which shows the direct visual field and indirect visual field in the cross section at the time of use of a concave mirror. It is explanatory drawing of the method of calculating the three-dimensional indirect visual field at the time of use of a concave mirror. It is a light ray distribution map on the reference surface where the light rays through the concave mirrors M1 and M2 reach.

Explanation of symbols

2 Sample stage 4 Biological sample 6 Two-dimensional detector 8 Main imaging lens 10 Fluorescence side filter 12, L1 to L5 Auxiliary imaging lens 14a, 14b, 24, 38, 46 Light source holder 16 Direct field of view of two-dimensional detector 18 Indirect field of view of two-dimensional detector 18A Indirect field of view reflected through reflector M1 when using a concave mirror 18B Indirect field of view reflected through reflector M2 when using a concave mirror 18C Distribution map of rays reaching via mirror M1 18D Reflection 28 A continuous spectrum light source 30 A condensing lens 32a, 32b, 36 An optical fiber 34 An interference filter disk 34a An interference filter 40 A stepping motor 42 A pulley 44 A belt A to F Light sources M1 to M5 Reflectors S1 to S5 Light source

[Example 1]
An embodiment of the biological image acquisition apparatus of the present invention will be described below. FIG. 1 is a diagram schematically showing the configuration of an embodiment of an apparatus capable of observing a biological sample from two directions.

  A biological sample 4 (small animal) is placed on the transparent sample stage 2, a two-dimensional detector 6 such as a CCD camera is disposed directly above the biological sample 4, and the two-dimensional detector 6 has a detection surface side. A main imaging lens 8 is arranged. A fluorescent filter 10 that transmits only the fluorescent component from the biological sample 4 is disposed between the main imaging lens 8 and the biological sample 4 as necessary. Reflecting mirrors M <b> 1 and M <b> 2 for guiding the light of the image on the back surface side (180 ° direction) of the biological sample 4 to the main imaging lens 8 are disposed below the sample stage 2.

  The light source device for irradiating the biological sample 4 with light has a light source holding unit that holds the light source units S1 to S4 at equal intervals on a circumference centered on one point on the body axis extension line on the head side of the biological sample 4. 14a and a light source holding part 14b for holding the light source parts S1 ′ to S4 ′ (not shown) at equal intervals on a circumference centered on one point on the body axis extension line on the tail side of the biological sample 4. . In FIG. 1, only the circumferential portions that hold the light source portions S1 to S4 and S1 'to S4' are shown as the light source holding portions 14a and 14b.

  According to the above configuration, the front (0 °) and back (180 °) images as shown in FIG. 2 can be taken simultaneously by the two-dimensional detector 6. That is, the light of the front image of the biological sample 4 and the light of the back image of the biological sample 4 reflected by the reflecting mirrors M1 and M2 are imaged by the main imaging lens 8 under the two-dimensional detector 6, and two-dimensional detection is performed. The two images are projected on the device 6 at the same time. The image on the back side is slightly smaller than the image on the front side because the optical path length is longer than that of the image on the front side. Further, since the optical path lengths from the reflecting mirrors M1 and M2 are different, blur is generated on the two-dimensional detector 6, but by inserting a weak auxiliary concave lens 12, it is possible to focus on each observation direction.

  The relationship between each light source part S1-S4, S1'-S4 'of the light source device and the field of view of the two-dimensional detector 6 is shown in FIGS. 3A and 3B. In these figures, the dark hatched portion 16 indicates the direct field of view of the two-dimensional detector 6, and the thinner hatched portion 18 indicates the indirect field of view through the reflectors M1 and M2 of the two-dimensional detector 6. In this example, the reflecting mirrors M1 and M2 are obliquely below the biological sample 4 as an optical system for guiding the image light viewed from the 144 ° direction and the 212 ° direction of the biological sample 4 to the main imaging lens 8. The two-dimensional detector 6 can simultaneously acquire images from a total of three directions in which the images of the front surface (0 °) of the biological sample 4 are combined. As shown in these drawings, each of the light source parts S1 to S4, S1 ′ to S4 ′ is placed in any of the direct visual field 16 and the indirect visual field 18 of the two-dimensional detector 6 at an oblique position with respect to the biological sample 4. It is arranged at a position that does not enter. Since the light sources S1 to S4 and S1 ′ to S4 ′ do not exist within the range of the direct field 16 and the indirect field 18 of the two-dimensional detector 6, direct light reflection of the light sources S1 to S4 and S1 ′ to S4 ′ is reflected. There is no problem such as blooming due to backlight. 3 and FIG. 1 are different in the arrangement of the reflecting mirrors M1 and M2, but the arrangement positions of the light source portions S1 to S4 and S1 'to S4' are set in the same manner.

Here, the observation direction and the irradiation direction are independent. In the apparatus design, it can be selected from two-direction observation, two-direction irradiation, three-direction observation, four-direction irradiation, five-direction observation, five-direction irradiation, etc. 3 and FIG. 5 described later show examples of different combinations.
In FIG. 3 as well, only the circumferential portions that hold the light source portions S1 to S4 and S1 ′ to S4 ′ are shown as the light source holding portions 14a and 14b.

  Returning to FIG. 1, each of the light source units S1 to S4 and S1 'to S4' will be described. Each light source part S1-S4, S1'-S4 'is provided with the light source of A-C, respectively. The light source A is a white LED, emits visible light between 400 nm and 700 nm, and has a spatial irradiation angle that illuminates the whole biological sample 4. The light sources B and C are both fluorescence excitation light sources, but have different excitation wavelengths. The light source B is, for example, a laser diode (hereinafter referred to as LD) that emits light having a wavelength of 690 nm, and the light source C is, for example, light having a wavelength of 780 nm. LD that emits light.

  FIG. 4A shows a specific configuration example of each light source unit S1 to S4, S1 ′ to S4 ′.

The light source A is a white LED for illuminating the biological sample 4 and capturing an appearance image. Source B, C is a fluorescence excitation light source, the light source B and the light emitting element LDramuda ₁ that emits excitation light having a wavelength of lambda _1, consisting of the excitation-side interference filter Fexramuda ₁ attached to the light-emitting side of the light emitting element LDλ _1. The light source C includes a light emitting element LDλ ₂ composed of an LD that emits excitation light having a wavelength λ ₂ , and an excitation side interference filter Fexλ ₂ attached to the light emitting side of the light emitting element LDλ ₂ . However, the light sources B and C can add a diverging lens (not shown) for irradiating the whole biological sample 4 after the interference filters Fexλ ₁ and Fexλ ₂ as necessary. Here, the selection of the three types of light sources A, B, and C shown in FIG. 4A can be performed simply by turning on and off the lighting power source without mechanical switching. Therefore, the light source directions (S1 to S4, S1) are switched without mechanical switching by turning on / off the light sources A, B, and C disposed in the directions S1 to S4 and S1 ′ to S4 ′. 'To S4) and the type of light source (A, B, C) are designated.

Next, characteristics of the excitation light source and the excitation interference filter will be described with reference to FIG. 4B. FIG. 4B shows the relationship between the light emitting element LDλ ₁ of the light source B and the interference filter Fexλ ₁ attached to the light emitting side.

The light-emitting element LDλ ₁ tends to be thought to emit only light having a single wavelength λ ₁ , but actually involves light emission with a weak tail. The skirt portion includes a wavelength component that passes through the fluorescence-side filter 10 provided on the incident side of the two-dimensional detector 6. When light having such a wavelength is irradiated toward the biological sample 4. The fluorescence component generated in the biological sample 4 passes through the fluorescence side filter 10 and enters the two-dimensional detector 6. As a result, stray light due to leakage light components other than the fluorescence of the sample overlaps with the captured fluorescent image, and the detection sensitivity of fluorescence is lowered.

Therefore, in this embodiment, by attaching the interference filter Fexramuda ₁ for blocking light of skirt portion of the emission wavelength on the light emission side of the light emitting element LDramuda _1, excitation light from the light emitting element LDramuda ₁ in transmission region of the fluorescence side filter 10 Ingredients are removed. As a result, only the fluorescent component from the biological sample 4 is transmitted through the fluorescent filter 10, and a decrease in the fluorescence detection capability due to stray light being mixed into the captured image on the two-dimensional detector 6 can be prevented.

  Although the light source B has been described above, the light source C has the same configuration as the light source B.

  In this configuration, that is, each light source is a laser diode LD or light emitting diode LED, and an optical filter that shields light at the bottom of the emission wavelength, such as an interference filter, for each LD or LED. The provided fluorescence excitation light source can achieve a remarkable effect that it is possible to prevent a decrease in fluorescence detection capability due to stray light being mixed into a captured image on the two-dimensional detector 6.

  In the example shown in FIGS. 1 and 3, the two light source holding portions 14a and 14b are arranged. However, the present invention is not limited to this, and there is only one light source holding portion. Also good.

  Moreover, in said Example, although each light source part S1-S4, S1'-S4 'is comprised by the light source of A-C, respectively, it is each by one light source A for illumination and one excitation light source B or C. The light source units S1 to S4, S1 ′ to S4 ′ may be configured, or each of the light source units S1 to S4 and S1 ′ to S4 ′ may be configured by only two excitation light sources B and C, depending on the application. The light source units S1 to S4 and S1 ′ to S4 ′ may be configured.

  Next, the operation | movement at the time of the fluorescence image measurement by the biometric image acquisition apparatus shown in FIG. 1 is demonstrated.

  First, in a state where the fluorescent filter 10 is not disposed in front of the main imaging lens 8, only the light source A (white LED) for illumination is turned on in all the light source portions S1 to S4 and S1 'to S4'. By photographing with the two-dimensional detector 6 in this state, the appearance image of the biological sample 4 can be acquired.

Next, a fluorescence side filter 10 in which a transmission wavelength range corresponding to the emission wavelength λ ₁ (for example, 690 nm) of the light source B is arranged in front of the main imaging lens 8, and all the light source parts S 1 to S 4, S 1 ′ to Only the excitation light source B is turned on in S4 ′. By taking an image with the two-dimensional detector 6 in this state, an image of fluorescence excited by excitation light having a wavelength of λ ₁ can be acquired.

Next, the fluorescence side filter 10 in front of the main imaging lens 8 is set to a transmission wavelength range corresponding to the emission wavelength λ ₂ (for example, 780 nm) of the light source C, and in all the light source parts S1 to S4, S1 ′ to S4 ′. Only the excitation light source C is turned on. By photographing with the two-dimensional detector 6 in this state, an image of fluorescence excited by excitation light having a wavelength of λ ₂ can be acquired.

  The image acquired by the two-dimensional detector 6 includes two kinds of images of 0 ° (front) and 180 ° (back) as shown in FIG. A total of six types of images can be acquired.

  In the shooting performed by turning on the light source B or C, in the above method, all the light sources B or the light sources C are turned on at the same time to capture fluorescent images of four-direction simultaneous irradiation. There is also a method in which each of the light sources C is turned on one by one in order and photographing is performed each time. Thus, front and back fluorescent images are obtained for each of the four irradiation directions. In this method, it takes time to complete all photographing, but since the appearance of fluorescence differs depending on the irradiation direction, more various fluorescent images can be obtained by combining the irradiation direction and the imaging direction.

  On the other hand, in the case of light emission image measurement, all light sources are turned off to obtain light emission images, and appearance image shooting is performed with only the light source A turned on.

[Example 2]
An embodiment of a biological image acquisition apparatus capable of simultaneously capturing images from five directions of a biological sample will be described. FIG. 5 is a block diagram schematically showing an embodiment of a biological image acquisition apparatus that can observe a biological sample simultaneously from five directions.

  A biological sample 4 (small animal) is placed on the transparent sample stage 2, a two-dimensional detector 6 such as a CCD camera is disposed directly above the biological sample 4, and the two-dimensional detector 6 has a detection surface side. A main imaging lens 8 is arranged. A fluorescent filter 10 that transmits only the fluorescent component from the biological sample 4 is disposed between the main imaging lens 8 and the biological sample 4 as necessary. The light of the image seen from the position of 72 °, 144 °, 216 °, 288 ° (front (0 o'clock direction) is 0 °) of the biological sample 4 is reflected around the sample stage 2 counterclockwise. Reflecting mirrors M2, M3, M4 and M5 leading to the main imaging lens 8 are arranged. On each optical path from the reflecting mirrors M2, M3, M4, and M5 to the main imaging lens 8, auxiliary imaging lenses L1 to L5 for eliminating defocus due to the optical path length difference are arranged. In this embodiment, the auxiliary imaging lenses L1 to L5 are mosaic lenses.

The light source device that irradiates light to the biological sample 4 is a light source holding unit that holds the light source units S1 to S5 at equal intervals on a circumference centered on a point on the body axis extension line on the head side of the biological sample 4. 24. The light source unit S1 is arranged so as to irradiate light obliquely in the 0 ° direction with respect to the biological sample 4, and the light source units S2 to S5 are arranged counterclockwise from the light source unit S1 at intervals of 72 °. That is, the light source units S2 to S5 are arranged corresponding to the observation angles by the reflecting mirrors M2 to M5 . The light source units S1 to S5 include light sources A to C as in the configuration of FIG. Similarly to the example shown in FIG. 3, the light source holding unit 24 and each of the light source units S1 to S5 are both in the direct visual field of the two-dimensional detector 6 and the indirect visual field through the reflectors M2, M3, M4, and M5. It is placed in a position that does not enter. In FIG. 5, only the circumferential portion that holds the light source parts S <b> 1 to S <b> 5 is illustrated as the light source holding part 24.

  According to said structure, the light of the image from observation angles 72 degrees, 144 degrees, 216 degrees, and 288 degrees other than the 0 degree direction from the biological sample 4 arrange | positioned on the sample stand 2 is each reflective mirror M2, M3. , M4, M5, and imaged on the common two-dimensional detector 6 by the imaging lens 8. Since light from each observation angle reflected by each reflecting mirror M2, M3, M4, and M5 has a different optical path length, weak auxiliary imaging lenses L1 to L5 having different focal lengths are inserted for each viewing angle. , Focus shift can be eliminated. In this way, the two-dimensional detector 6 is formed with an image viewed from five directions of the biological sample 4 as shown in FIG.

  In this embodiment, the light source device is configured by one light source holding unit 24 on the head side of the biological sample 4, but a light source holding unit may also be provided on the tail side of the biological sample 4. If it does so, it will become possible to irradiate light more uniformly from the both sides of the head side and the tail side with respect to the biological sample 4, and the shadow part can be reduced.

Further, in this embodiment, the light source holding unit 24 holds five light source units S1 to S5 that emit light from an angle corresponding to the image capturing direction with respect to a configuration for acquiring images from five directions of the biological sample 4. However, the number of observation directions and the number of irradiation directions do not necessarily match, and four or less or six or more light sources may be held by the light source holding unit 24. Further, although the irradiation angles of the five light sources in the present embodiment are made to coincide with the observation angles, the angles are also arbitrary, for example, 36 °, 108 °, 180 on the circumference of the light source holding unit 24. It is also possible to adopt a configuration in five directions of °, 252 °, and 312 °. In the configuration using an intermediate irradiation angle in the observation direction, in this case, for example, in the observation in the 0 ° direction, when the light source of 36 ° and 312 ° is turned on, the samples are averagely illuminated from the front, and 180 ° When only one light source is turned on, it is illuminated from the back side and observed from the opposite 0 ° direction. Similarly, in the 72 ° observation direction, the front illumination is 36 ° and 108 ° , and the back illumination is 252 °.

  In addition, about the operation | movement at the time of the fluorescence image measurement by the biometric image acquisition apparatus of this Example, it is the same as the operation | movement of Example 1, and detailed description here is abbreviate | omitted.

  FIG. 7 is an appearance image captured so that the light source units S1 to S5 intentionally enter the direct visual field or the indirect visual field of the two-dimensional detector 6 in the biological image acquisition apparatus shown in FIG. Shows what happens. In this image, five appearance images viewed from the directions of 72 °, 144 °, 216 °, and 288 ° counterclockwise with the direction (front direction) seen from the top of the biological sample 4 as 0 ° are simultaneously two-dimensionally detected. It was copied by the vessel 6.

  The 0 ° image is an image taken directly from above the biological sample 4 through the auxiliary coupling lens L1 and the main imaging lens 8. In photographing from the 0 ° direction, light irradiation from the light source parts S1, S2, S5 above the sample stage 2 is not a problem, but the light source parts S3, S4 below the sample stage 2 are transparent. The direct light transmitted through the sample stage 2 is reflected on the two-dimensional detector 6 as a strong light spot P.

  In shooting from the 72 ° direction, light from the light source unit S4 is reflected as a light spot Q on the two-dimensional detector 6 via the reflecting mirror M2, and in shooting from the 288 ° direction, light from the light source unit S2 is reflected. The light spot T is reflected on the two-dimensional detector 6 via the mirror M5. In the case of photographing from the 144 ° direction, the light from the light source unit S5 is reflected as a light spot R on the two-dimensional detector 6 via the reflecting mirror M3, and in the case of photographing from the 216 ° direction, the light from the light source unit S1. Is reflected as a light spot S on the two-dimensional detector 6 through the reflecting mirror M4. In particular, it can be seen that the light spots P, R, and S reflected at 0 °, 144 °, and 216 ° shine not only in the original light spot but also in a cross shape. This is caused by excessive charge being generated in the light receiving element that has received extremely strong light, and in addition to saturation of the light receiving element, the charge has flowed to the adjacent light receiving element, which is called blooming. Figuratively speaking, this is a phenomenon similar to the case where lens halation occurs when shooting in the backlit state where the sun is reflected. When blooming occurs, the image of that part is destroyed, and even if blooming does not occur, the place where light is not originally emitted moves as a light spot, so an accurate image cannot be obtained.

  Therefore, as shown also in this embodiment, the light source sections S1 to S5 are arranged at positions that do not enter either the direct field of view or the indirect field of view of the two-dimensional detector 6, so that the unnecessary light spot as described above is obtained. Is not reflected in the captured image, and a clear observation image can be acquired.

  In the first and second embodiments described above, each excitation light source of the light source device is configured by a combination of a laser diode and an interference filter, but a filter capable of switching the transmission wavelength band of light from one light emitting element is used. Alternatively, the wavelength of the excitation light may be selectively switched and the excitation light may be distributed to each excitation light source. FIG. 8 shows an example of the configuration of such a light source device.

  In the example of FIG. 8, a condensing lens 30 is arranged on the light emission side of a light source 28 having a continuous emission spectrum, for example, a halogen lamp, and the continuous spectrum light emitted from the light source 28 is guided to the entrance of the optical fiber 32a. On the exit side of the optical fiber 32a, a plurality of interference filters 34a having different transmission wavelength bands are provided in the circumferential direction, and a filter disk 34 that switches the interference filters 34a by rotating itself is provided. Only light of an arbitrary wavelength band can be extracted from the continuous spectrum emitted from the fiber 32a. An optical fiber 32b is also provided on the exit side of the interference filter 34a of the filter disc 34, and the optical fiber 32b is branched into a plurality of optical fibers 36 (four in this example) that guide light to each pumping light source on the way. After that, the tip of the branch fiber is guided to a position in place of the light source B of S1, S2, S3, and S4 shown in FIG. 1, and the tip of each fiber is irradiated toward the sample 4.

The continuous spectrum light from the light source 28 is selectively extracted by the interference filter 34a selected in the filter disk 34 and is supplied to each excitation light source. In this method, since the wavelength of the excitation light is switched by the filter disk 34 that is a wavelength selection filter, excitation light having a plurality of wavelengths can be emitted from one excitation light source. Therefore, only one excitation light source for irradiating the biological sample 4 with the excitation light is required for each light source unit . That is, in FIG. 1, each of the light source units S1 to S4 and S1 ′ to S4 ′ on the light source holding units 14a and 14b includes light sources B and C that emit excitation light having different wavelengths as excitation light sources. If it is the system of 8, the light source should just have either B or C. However, in this method, since light simultaneously travels through the plurality of optical fibers 36, it is impossible to turn on the plurality of light sources independently at different timings. On the other hand, since the filter 34a of various kinds of transmission wavelength bands can be arranged on the filter disc 34, the number of excitation wavelengths to be selected can be easily increased. As a modified example, if one of the filters mounted on the filter disc 34 is a neutral filter instead of an interference filter of a specific wavelength, and a light obtained by reducing the light of the halogen lamp by an appropriate amount is guided to the irradiation position, The irradiated light can be used for external illumination. That is, it can be used in place of the dedicated appearance image illumination light source A.

  As described above, as an example of the external illumination light source, the case of the white LED shown by the light source A in FIGS. 1 and 4A and the case where the halogen lamp in FIG. Here, the requirements of the external illumination light source can be summarized: 1) all or part of the wavelength component of the illumination light may be entered into the two-dimensional detector without being removed by the filter 8 before entering the two-dimensional detector; and 2) If the sample is very bright as the fluorescence excitation light source, the diffuse reflected light of the sample is too strong and the detector is saturated. Therefore, the illumination light is sufficiently dimmed. . Therefore, if this requirement is satisfied, methods other than the above-described embodiments are possible. For example, instead of a white LED, even a fluorescent excitation LD or LED is lit weakly to illuminate the sample, and external illumination By selecting the wavelength characteristics of the filter 8 in front of the two-dimensional detector so that a part of the wavelength of the LD or LED is intentionally passed only at times, it is possible to use both the external illumination light source and the fluorescence excitation light source. It is.

  In the first and second embodiments described above, an example in which an image of the biological sample 4 viewed from multiple directions is formed on one two-dimensional detector 6 and simultaneously acquired is shown. As shown in FIG. 9, an image of the biological sample 4 viewed from multiple directions may be acquired using a plurality of two-dimensional detectors. In FIG. 9, the directions of 0 ° and 90 ° are photographed by the first two-dimensional detector 6, and the directions of 180 ° and 270 ° are photographed by the second two-dimensional detector 6 '. Although illustration in FIG. 9 is omitted, even in such a configuration, each light source of the light source device that irradiates light to the biological sample 4 is a direct field of view of any two-dimensional detector (with a reflector). When it does, it must be arranged in a position that does not even enter its indirect field of view, and it must be configured so that the direct light of those light sources is not reflected in all two-dimensional detectors.

  In the example of FIG. 9, a two-dimensional detector 6 ′ is further provided at a position different from the two-dimensional detector 6 disposed immediately above the sample stage 2, and reflecting mirrors M <b> 1 and M <b> 2 are provided. An image at 0 ° in front of the biological sample 4 is acquired by the two-dimensional detector 6 directly above the biological sample 4, and an image at 90 ° is acquired by the two-dimensional detector 6 as reflected light from the reflecting mirror M2. 4 is acquired by the two-dimensional detector 6 ′ as reflected light from the reflecting mirror M1, and an image of 270 ° is acquired directly from the biological sample 4 by the two-dimensional detector 6 ′. Yes.

  Further, in the light source device that irradiates light to the biological sample 4, as described above, if the types of excitation light sources that can be irradiated are increased to broaden the selection range of excitation wavelengths, various fluorescent dyes can be obtained. On the other hand, it is possible to select a light source having an optimum wavelength. Although an example of such a light source device has already been described with reference to FIG. 8, a single light source can be configured with more types of excitation light sources separately from the method. FIG. 10 and FIG. 11 each show an example.

  In the example of FIG. 10, six light sources A to F constituting the light source units S <b> 1 to S <b> 4 are held by the light source holding unit 46 on a double circumference. The light sources A to C of the light source sections S1 to S4 are held on a circumference perpendicular to the plane of the sample table 2 around the point on the body axis extension line on the head side of the biological sample 4, and the circle The light sources D to F are held on a concentric circle inside the circumference. In this case, the light emitting part A can be a white LED used when an appearance image of the biological sample 4 is taken, and the remaining light emitting parts B to F can be LDs or LEDs for excitation light sources that excite fluorescence. In this way, if the light source holding unit 46 holds the light source on the multiple circumferences, the space of the two-dimensional detector (not shown) in the direct visual field and the indirect visual field can be effectively used. More types of excitation light sources can be arranged.

  In the example of FIG. 11, the light source units S1 to S4 each having six light sources A to F are in relation to the plane of the sample table 2 centered on a point on the body axis extension line on the head side of the biological sample 4. It is held by the light source holding part 38 on a vertical circumference. The light sources A to F of the light source units S1 to S4 are arranged in a line on the same circumference. The light source holding part 38 is supported by a support mechanism (not shown) so as to be rotatable around the center of the circumference where the light source parts S1 to S4 are held. The light source holding unit 38 is configured to be rotationally driven via a belt 44 by a driving mechanism including, for example, a stepping motor 40 and a pulley 42. In this example, the light source to be lit can be moved to a predetermined position by driving the stepping motor 40. Therefore, even when a large number of light sources are arranged side by side on the same circumference, a desired wavelength can be obtained from the predetermined position. It is possible to irradiate the light. In FIG. 11, since the four light source parts S1 to S4 are arranged at equal intervals on the same circumference, the maximum rotation angle of the light source holding part 38 may be 90 °. By combining the structure for rotating the light source holding unit and the structure for arranging the light sources on the multiple circumferences shown in FIG. 10, more types of light sources can be used for the direct field and the indirect field of the two-dimensional detector 6. It becomes possible to provide in the position which does not enter.

  As described above, the illuminating device of the biological image acquisition device may be used for appearance image photography or as an excitation light source for fluorescence image photography. Among these, in the appearance image photographing, a light source such as a white LED is turned on to illuminate the biological sample 4, but measurement is performed without inserting a filter for removing the illumination light wavelength component into the two-dimensional detector on the light receiving side. That is, the wavelength component included in the illumination light is directly incident on the two-dimensional detector. For this reason, if the illumination light source is within the field of view of the two-dimensional detector, very strong direct light is incident on the two-dimensional detector, causing problems such as blooming. As described above, in the biological image acquisition apparatus of the present invention described above, the light source is arranged at a position that does not enter either the direct visual field or the indirect visual field of the two-dimensional detector. Direct light does not enter the two-dimensional detector, and troubles such as blooming do not occur.

On the other hand, in fluorescence image capturing, the excitation light applied to the sample is obtained by removing the wavelength component transmitted through the fluorescence filter 10 by the interference filter, so that the excitation light source is in the field of view of the two-dimensional detector. However, it should be removed by the fluorescent filter 10 before entering the two-dimensional detector. For this reason, even if the irradiation point is directly projected on the two-dimensional detector, theoretically, the intensity of the corresponding light should be zero and no problem should occur. However, actually, the light rejection rate other than the transmission wavelength band of the interference filter is not 0, and leaked light of about 10 ⁻⁶ to 10 ⁻⁸ is generated. If the irradiation point is in a position directly projected onto the two-dimensional detector due to the leaked light, the irradiation point is reflected although not as much as blooming. In particular, in the light source device shown in FIG. 8, in order to remove light in a predetermined wavelength band from a continuous light source such as a halogen lamp by an interference filter, the light emitted from the LD that is a single wavelength light source as shown in FIG. The amount of leakage light is greater than when light in the bottom wavelength band is removed by an interference filter, and direct light transfer from the light source is likely to occur.

  To summarize the above, the degree of inconvenience when the irradiation point is directly projected onto the two-dimensional detector is the largest when the appearance image is acquired, and the next is when the continuous light source is used when acquiring the fluorescent image, and the influence is relatively small. This is the case of fluorescence image acquisition using a single wavelength light source such as an LD. However, in any case, as long as the light source is placed at a position that does not fall in either the direct field or the indirect field of view of the two-dimensional detector, the problem of reflection of the irradiation point can be avoided. The technique of the present invention is effective.

  In addition, when a large number of reflecting mirrors are arranged to simultaneously acquire images from more directions, it is necessary to arrange the reflecting mirrors densely. In such a case, even if it is attempted to irradiate light from the same direction as the observation direction of the reflecting mirror, it is difficult to arrange many excitation light sources in the gap between the reflecting mirror and the reflecting mirror. Even in such a case, it is possible to arrange many types of excitation light sources by arranging the light sources so as to irradiate the biological sample 4 with light from an oblique direction as in the embodiments in the present specification. .

  In addition, in each Example of FIG.1, FIG.3, FIG.5, FIG.10, FIG.11, in order to make explanation easy to understand, the example which has arrange | positioned the two-dimensional detector and the lens right above the sample was shown. Even if the entire apparatus is tilted at an appropriate angle, for example, 45 degrees or 90 degrees, the same can be considered. In that case, the concept of “upper side and lower side of the sample” disappears. That is, it can be said that the image on the upper side of the sample in the above embodiment is generally the image on the two-dimensional detector side of the sample. The “two-dimensional detector side image” means an image that can be directly seen from the direction in which the two-dimensional detector is arranged. On the other hand, the lower image can be said to be “an image that can be directly seen from other directions” with respect to the “two-dimensional detector side image”. Here, the lower image is not limited to an image in a 180 ° direction when the direction of the two-dimensional detector is 0 °. For example, in FIG. 5, the images for the two directions of 144 ° and 212 ° are the lower images, so the images of 144 ° and 212 ° are the images opposite to the two-dimensional detector.

  When the direction between the direction of the two-dimensional detector and the observation direction is defined as the “direction on the two-dimensional detector side” from 0 ° to 90 °, the angle between the direction of the two-dimensional detector and the observation direction is 90 °. The direction that exceeds 270 ° and does not exceed 270 ° can be defined as “other direction”. In other words, “the other direction” is an obtuse angle between the observation direction and the direction of the two-dimensional detector. is there. The backlight problem at the time of multi-directional simultaneous observation, which was one of the problems to be solved by the present invention, occurs when the angle formed by the observation direction and the direction of the two-dimensional detector is an obtuse angle. By disposing the irradiation light source outside the range of the field of view of the two-dimensional detector, the inconvenience is solved.

  In addition, if a plurality of two-dimensional detectors are used, an image on the opposite side of one of the plurality of two-dimensional detectors can be observed with the same two-dimensional detector as in FIGS. It can be observed with another two-dimensional detector detector as shown in FIG. In FIG. 9, the first two-dimensional detector observes the directions of 0 ° and 90 °, and the second two-dimensional detector observes the directions of 180 ° and 270 °, so that the four directions are simultaneously measured by two two-dimensional detectors. Observing. In general, since a two-dimensional detector is expensive, it is desirable to use a single two-dimensional detector to observe all directions. However, an apparatus that observes four directions using two two-dimensional detectors has four two-dimensional detectors. It is worth using multiple detectors because it is cheaper than a device that uses detectors. This is an example of a measurement system using a plurality of two-dimensional detectors whose number is smaller than the number of observation directions. If a plurality of two-dimensional detectors are used, the total light receiving area of the detector can be made larger than that of a single detector. Therefore, even if it is a little expensive, it is advantageous in detecting weak light such as luminescence measurement. It was mentioned that there could be an option to perform all imaging directions with multiple 2D detectors.

  In addition, if FIG. 1 is tilted 90 ° to the right and only the sample stage is left horizontal, the two-dimensional detector will be on the right side of the sample, so the front (0 °) image viewed from the two-dimensional detector is the right side of the sample. The image, the back surface or the opposite image (180 ° image) is the left image of the sample. In this case, the two-dimensional detector is disposed in the right tangential direction of the sample stage.

[Example 3]
An example in which a concave mirror is employed as the reflecting mirror will be described with reference to FIGS.

  FIG. 12 is a perspective view when the plane mirrors M1 and M2 in the first embodiment shown in FIGS. 1, 3A and 3B are replaced with concave mirrors. The important point here is that the center of curvature of the concave mirror M1 is set to C1 (shown by a black dot in the figure) next to the antinode of the sample 4. The position C1 is at a distance equal to the sample when viewed from the lens 8. In this way, an oblique lower left image of the sample by the concave mirror M1 as seen from the head of the sample can be formed at a position 4A adjacent to the sample 4. Similarly, by setting the center of curvature of the concave mirror M2 to a position C2 that is at the same distance as the sample when viewed from the lens 8, an image on the oblique lower right side of the sample by the concave mirror M2 can be formed at a position 4B adjacent to the sample 4. The sample 4 and the image formed on the side of these samples are almost the same size as the original sample, and the directions of the head and tail are reversed. Since the sample and the three images 4A and 4B are arranged at an equal distance when viewed from the lens 8, they can be simultaneously focused on the CCD 6 and photographed.

  On the other hand, when a plane mirror as shown in FIGS. 3A and 3B is used, since the image on the back side can be far from the camera lens, the three members do not line up at the same distance from the camera lens. For this reason, there are two disadvantages: the inability to focus on all three persons, and the image that can be made far away is smaller than the sample. These two drawbacks are great advantages because they can be removed by replacing the reflecting mirror with a concave mirror. That is, if all three members are at the same distance, the lens 8 is in focus even in a bright state, and a lens with a small F number can be used when receiving weak light from the sample. . The auxiliary imaging lens 12 disclosed in the first and second embodiments also has a function of moving the focal position of an image that can be distant, but a function that directly aligns the size of an image formed far away to the image. Lacks. Furthermore, because of the limitation of the size of the auxiliary lens, the auxiliary lens system has a drawback that it is difficult to use the main imaging lens with a small F number, and the effect of using the concave mirror of Example 3 is remarkable.

  Next, a description will be given on the light source side. S1, S2, S3 and S4 are the light source units described in the above embodiments. The position where the light source unit is arranged is a problem, and depending on the location, the reflection of the light source occurs.

  FIG. 13 is a cross-sectional view showing a direct field and an indirect field of the two-dimensional detector when the reflecting mirror is a concave mirror. Here, the region 16 is a direct field of view of the two-dimensional detector, and is the same as FIG. 3B. When there is no reflector, no reflection occurs if the light source is directly outside the field of view. A region 18 (including both regions 18A and 18B) is an indirect field of view when there is a concave reflector, and shows a range reflected on the two-dimensional detector via the concave reflector. Of these, the region 18A is an indirect field of view reflected through the reflecting mirror M1, and the region 18B is an indirect field of view reflected through the reflecting mirror M2.

  Although the indirect field of view by the concave reflecting mirror in the cross-sectional view can be relatively easily obtained as shown in FIG. 13, the problem is the estimation of the indirect field of view of the portion deviated from the cross-section. In the case of a plane mirror, as shown in FIG. 3A, light sources S1, S2, S3, and S4 are arranged in a cross section perpendicular to the body axis centered on a point on the extension of the body axis of the sample to avoid reflection. However, in the case of a concave mirror, evaluation of a three-dimensional visual field is somewhat difficult.

  A calculation method for obtaining a three-dimensional indirect field of view will be described with reference to FIG. In this calculation, a large number of light beams are emitted from the center 8A of the lens 8 (so-called lens principal point) toward the concave mirror M1. Here, as an example, one of the rays is 8A-U. Point U is a point on the concave mirror M1. A large number of light beams such as the light beam 8A-U travel obliquely upward after being reflected by the concave mirror M1, but considering a reference plane REF (a horizontal plane at a height H from the sample) for evaluation, a large number of light beams ( One of them is U-V), so that a distribution map of the hit points V can be obtained. Similarly, a distribution map can be obtained with the reflecting mirror M2. FIG. 15 is a distribution diagram thus obtained. In FIG. 15, the distribution diagram 18C on the right side is a distribution diagram in which light rays reach through the reflecting mirror M1, and the distribution diagram 18D on the left side is a distribution diagram in which light rays through the reflecting mirror M2 arrive. Therefore, if the light sources S1, S2, S3, and S4 are placed outside the range of the light distribution, the reflection of the indirect field of view can be avoided. Of course, the direct field of view can be easily understood, and thus the arrangement in which all the light sources S1, S2, S3, S4 are placed outside the direct field and the indirect field of view is the case where the reflecting mirror is a concave mirror. Is also possible.

  Actually, as can be seen from FIG. 15, since the indirect field of view of the corner portion of the reflector extends obliquely, it is necessary to arrange the light source while avoiding this portion.

  The case where there are two concave mirrors has been shown. Similarly, when optical elements such as concave mirrors and plane mirrors are combined, a large number of light beams are emitted from the principal point of the lens toward each optical element, and the distribution on the reference surface is reduced. Since the indirect field of view can be obtained by calculation, even in multi-directional simultaneous observation devices of various combinations including plane mirrors and concave mirrors, it is possible to reflect the light source by selecting the light source position avoiding the direct field and indirect field of view. It is possible to construct a device for obtaining clear, multidirectional images.

Claims (17)

A sample stage on which a biological sample is placed;
A two-dimensional detector;
The light on the two-dimensional detector side from the sample on the sample table and the light in the other direction are guided to the two-dimensional detector, and the plurality of guided lights are guided on the two-dimensional detector. An imaging optical system that forms an image on the imaging optical system, comprising: a reflecting mirror that guides light in a direction other than the direction on the two-dimensional detector side to the two-dimensional detector ;
The direct field viewed from the two-dimensional detector and the indirect field viewed from the two-dimensional detector through the reflector are arranged outside the range of the field of view of the two-dimensional detector , and light is applied to the sample on the sample stage. And a light source device including a light source that directly enters light into at least a part of the reflecting mirror ;
A biological image acquisition apparatus comprising: an image display device that displays an image captured by the two-dimensional detector. Of the light emitted from the light source is defined as "interference light" light entering the detector is reflected by direct or an object other than the sample, among light emitted from the light source, the path to be reflected by the sample when finally defined as "measurement object light" light entering the detector via the imaging optical system and the light source device has a configuration in which the number of reflections of light of the measurement object is less than the number of reflections of the interference light The biological image acquisition apparatus according to claim 1.   The biological image acquisition device according to claim 1, wherein only one of the two-dimensional detectors is provided. A plurality of the two-dimensional detectors are provided,
Each two-dimensional detector is disposed at a position where it can directly receive light in different directions of the sample on the sample stage,
The biological image acquisition apparatus according to claim 1, wherein the imaging optical system is provided for each two-dimensional detector.   5. The biological image acquisition apparatus according to claim 1, wherein the light source device includes a light source holding unit that holds a plurality of light sources in a plane perpendicular to the body axis of the biological sample on the sample stage. .   The biological image acquisition device according to any one of claims 1 to 5, wherein the light source is a light source that illuminates a sample for acquiring an appearance image of the sample. The light source is an excitation light source that emits excitation light for generating fluorescence by exciting the sample when capturing a fluorescent image from the sample,
The said imaging optical system is arrange | positioned between the sample and the said two-dimensional detector, when imaging a fluorescence image, The filter which permeate | transmits only the light of the wavelength band of a fluorescence component is provided. The biological image acquisition device according to claim 1.   The light source is a light source that illuminates the sample to obtain an appearance image of the sample and / or an excitation light source that emits excitation light for exciting the sample and generating fluorescence when capturing a fluorescent image from the sample. The biological image acquisition device according to claim 1, wherein the plurality of types of light sources can be turned on or off independently.   The light sources are a plurality of types of light sources composed of excitation light sources that emit excitation light for generating fluorescence by exciting the sample when capturing a fluorescent image from the sample. The biological image acquisition device according to any one of claims 1 to 5, 7 or 8, further comprising a structure in which an optical filter is superimposed on each diode for each laser diode or light emitting diode.   10. The biological image acquisition according to claim 5, wherein the light source holding unit holds the light source on a circumference centered on a point on a body axis extension line of the biological sample on the sample stage. apparatus.   The biometric image acquisition apparatus according to claim 10, wherein the circumference includes two or more concentric circumferences having different radii.   The light source device further includes a support mechanism that rotatably supports the light source holding part about the circumference of the light source holding part that holds the light source, and a drive mechanism that rotates the light source holding part. The biological image acquisition device according to claim 10 or 11. The living body image acquiring apparatus according to claim 1 , wherein the reflecting mirror includes a plane reflecting mirror. The living body image acquisition according to any one of claims 1 to 13 , wherein the imaging optical system includes an auxiliary imaging lens that corrects a difference in optical path length of light of a plurality of images formed on the two-dimensional detector. apparatus. The reflector biometric image acquisition apparatus according to claim 1, 13 or 14 including a concave reflecting mirror. The biological image acquiring apparatus according to claim 15 , wherein the concave reflecting mirror is set so that a center of curvature is located at a side of the sample and at an equal distance from an imaging lens of the camera. The light source device includes a white light source, a wavelength selection filter that selectively transmits only light in a predetermined wavelength band among the light from the white light source, and an optical fiber that guides the light transmitted through the wavelength selection filter to the light source the provided, biometric image obtaining apparatus according to any one of claims 1 and selects the wavelength band of light emitted 16 from the light source by switching the wavelength band transmitted through the wavelength selective filter.