JP2020114452A - Illumination device, illumination method, and observation device - Google Patents

Abstract

To establish both of switching a wavelength band of irradiation light and obtaining an observation image having higher quality.SOLUTION: There is provided an illumination device comprising: a first light source unit for emitting wide-band light; a second light source unit for emitting narrow-band light having a wavelength band narrower than that of the wide-band light; a radiation angle change member for changing a radiation angle of the narrow-band light emitted from the second light source unit to generate a secondary light source; and a multiplexing member for multiplexing the wide-band light emitted from the first light source unit and the narrow-band light emitted from the second light source unit. The radiation angle change member changes the radiation angle of the narrow-band light so that incident angles of the wide-band light and the narrow-band light are closer to each other on an incident end surface of a light guide on which the light multiplexed by the multiplexing member is incident.SELECTED DRAWING: Figure 1

Description

The present disclosure relates to a lighting device, a lighting method, and an observation device.

In recent years, a laser is being used as a light source of an observation device for observing a surgical field of a patient such as an endoscope device or a microscope device, instead of a lamp light source that has been widely used so far. As an advantage of using a laser as a light source, for example, it is possible to expect low power consumption due to the high electro-optical conversion efficiency of the light source, and because the wavelength band is narrow, it can be specified by combining it with the light absorption characteristics of tissues such as blood vessels. It is possible to emphasize and observe the tissue. Furthermore, when a laser is used as a light source in an endoscope apparatus, for example, low power consumption can be expected due to high optical coupling efficiency with a light guide and high directivity of laser light can be used. A further advantage is that the efficiency of optical coupling to the diameter light guide is high and an endoscope insertion portion having a small diameter can be realized.

Here, in the observation using the laser beam, various techniques have been developed in order to improve the image quality of the observation image. For example, when an object is irradiated with laser light and the irradiation field is observed, bright and dark spot patterns may appear due to the high coherence of the laser light. This phenomenon occurs because random light interference occurs on the rough surface of the object, and an interference pattern having a random intensity distribution appears. Such a speckled pattern is called speckle noise, and can obstruct the observation of the irradiation field. Therefore, in order to suppress the generation of speckle noise and obtain a higher quality observation image, the techniques exemplified in Patent Documents 1 to 5 below have been proposed.

For example, Patent Document 1 below discloses an endoscope system that uses, as a noise reduction device, a bundle fiber in which a plurality of optical fibers having an optical path difference length equal to or longer than a coherence length are bundled.

For example, Patent Document 2 below discloses an endoscope light source device that uses a plurality of modules that output intensity-modulated laser light through optical fibers, bundles the optical fibers, and further optically couples the optical fibers into a single optical fiber. Has been done.

For example, Patent Document 3 below discloses an illuminating device including a high-frequency superimposing means that superimposes a high-frequency signal on a drive current supplied to a semiconductor laser that is a light source to cause multimode oscillation of the semiconductor laser.

For example, Patent Document 4 below discloses an endoscope in which a vibrating means for vibrating an optical fiber is arranged in an endoscope insertion portion.

For example, Patent Document 5 below discloses an endoscope system that performs image processing on the obtained captured image and outputs it as an observation image.

On the other hand, in the observation device, a normal observation mode in which the operative field is observed with light in a wide wavelength band such as white light, and fluorescence excited by light in a predetermined wavelength band (hereinafter, also referred to as narrow band light) There are some that can be switched between a special observation mode in which only the site in the surgical field where the fluorescence is emitted is intensively observed by detection. In such an observation device, the irradiation light is switched between white light and narrow band light in accordance with the switching of the observation mode.

Here, when the white light and the narrow band light are switched, it is desirable that these lights are guided on the same optical axis and irradiated to the surgical field. When white light and narrowband light are emitted by following different optical paths, the irradiation angle of white light and narrowband light with respect to the operative field may be different from each other, and normal observation is performed. There is a possibility that the visibility of the observation image by the user may deteriorate, such as the appearance of shadows changing between the observation image obtained in the mode (normal observation image) and the observation image obtained in the special observation mode (fluorescence observation image). Because there is.

As an observing device capable of switching between white light and narrow band light and irradiating these lights by being guided along the same optical axis, those exemplified in Patent Documents 6 to 9 below are available. Proposed.

For example, Patent Document 6 below discloses an endoscope device in which white light or laser light (that is, narrow band light) is guided on the same optical axis via a half mirror.

For example, in Patent Document 7 below, white light and laser light are combined on the same optical axis by a combining member configured by combining a transmissive portion that transmits white light and a reflective portion that reflects laser light. A light source device for an endoscope is disclosed.

For example, Patent Documents 8 and 9 below disclose an endoscope light source device in which white light or laser light is guided along the same optical axis via a dichroic mirror.

JP, 2008-043493, A JP, 2009-240560, A JP, 2010-042153, A JP, 2010-172651, A JP2012-005785A JP, 2009-131496, A JP, 2012-081133, A JP, 2005-342033, A JP, 2006-000157, A

However, in the above-mentioned Patent Document 1, a bundle fiber device in which the strand length is equal to or longer than the coherence length, in the above-mentioned Patent Document 2, a multiple fiber light source device and an intensity modulator, in the above-mentioned Patent Document 3, a high-frequency superimposing circuit, and in the above-mentioned Patent Document 4, the machine. The above-mentioned Patent Document 5 requires an image processing device and a further device in addition to the configuration for realizing the function as a light source, so that the entire device becomes large and speckle noise reduction ( That is, the cost for improving the image quality is required separately. Further, in the technologies described in Patent Documents 6 to 9, for example, reduction of speckle noise is not considered, and it is hard to say that sufficient consideration has been given to improving the quality of observed images.

As described above, in the observation device for observing the operative field of the patient, the technology for realizing both switching of the wavelength band of the irradiation light according to the observation application and obtaining a higher quality observation image is Until now, it has not been sufficiently examined. Therefore, the present disclosure proposes a new and improved illumination device, illumination method, and observation device that are compatible with switching the wavelength band of irradiation light and obtaining a higher quality observation image. To do.

According to the present disclosure, a first light source unit that emits broadband light, a second light source unit that emits narrowband light having a wavelength band narrower than the broadband light, and the light source unit that emits light from the second light source unit An emission angle changing member that generates a secondary light source by changing an emission angle of narrowband light, the broadband light emitted from the first light source unit, and the narrowband light emitted from the secondary light source. And a diverging member for diverging, wherein the radiation angle changing member has an incident angle between the wideband light and the narrowband light at an incident end face of a light guide on which the light multiplexed by the synthesizing member is incident. An illumination device is provided that changes the emission angle of the narrowband light so that the light source approaches the light source.

Further, according to the present disclosure, the broadband light is emitted from the first light source unit, the narrow band light having a wavelength band narrower than the broadband light is emitted from the second light source unit, and the emission angle changing member. To generate a secondary light source by changing the emission angle of the narrow band light emitted from the second light source section, and to combine the broadband light emitted from the first light source section by a combining member. And combining the narrow band light emitted from the secondary light source, the radiation angle changing member at the incident end face of the light guide on which the light combined by the combining member is incident. An illumination method is provided in which the emission angle of the narrow band light is changed so that the incident angles of the wide band light and the narrow band light are close to each other.

Further, according to the present disclosure, an illuminating device that outputs at least one of broadband light and excitation light with which the operative field of a patient is irradiated is provided, and the illuminating device includes a first light source unit that emits broadband light. A second light source unit that emits a narrowband light having a wavelength band narrower than that of the broadband light, and a secondary light source is generated by changing an emission angle of the narrowband light emitted from the second light source unit. The radiation angle changing member includes: a radiation angle changing member; and a combining member that combines the wideband light emitted from the first light source unit and the narrowband light emitted from the secondary light source. Changes the emission angle of the narrowband light so that the incident angles of the wideband light and the narrowband light are close to each other at the incident end face of the light guide on which the light combined by the combining member enters. A device is provided.

According to the present disclosure, a first light source unit that emits broadband light and a second light source unit that emits narrowband light having a wavelength band narrower than the broadband light are provided. Therefore, the wavelength band of the irradiation light can be switched by appropriately controlling the driving of these light source units. Further, a radiation angle changing member that changes the radiation angle of the narrow band light is provided on the optical path of the narrow band light emitted from the second light source unit in the plurality of wavelength bands. Since the emission angle of each narrow band light is unified by the emission angle changing member, color unevenness is reduced when irradiating the narrow band light or the light obtained by combining the narrow band light and the wide band light. It is possible to improve the quality of the observed image. As described above, according to the present disclosure, it is possible to switch the wavelength band of irradiation light and obtain a higher quality observation image at the same time.

As described above, according to the present disclosure, it is possible to switch the wavelength band of irradiation light and obtain a higher quality observation image at the same time. Note that the above effects are not necessarily limited, and in addition to or in place of the above effects, any of the effects shown in this specification, or other effects that can be grasped from this specification. May be played.

It is a figure which shows one structural example of the illuminating device which concerns on 1st Embodiment. It is explanatory drawing for demonstrating the structure of the light guide which the output light from the illuminating device shown in FIG. 1 injects. It is explanatory drawing for demonstrating the characteristic of the dichroic mirror of the illuminating device shown in FIG. It is explanatory drawing for demonstrating the characteristic of the dichroic mirror of the illuminating device shown in FIG. It is explanatory drawing for demonstrating the characteristic of the dichroic mirror of the illuminating device shown in FIG. It is a figure which shows the reduction effect of the speckle noise by the illuminating device which concerns on 1st Embodiment. It is a figure which shows one structural example of the illuminating device which concerns on 2nd Embodiment. It is a figure which shows one structural example of an illuminating device when both white light and laser light are combined as diverging light. It is a figure which shows one structural example of an illuminating device at the time of adding a light source of a further wavelength band. It is a figure which shows one structural example of the endoscope apparatus to which the illuminating device which concerns on 1st Embodiment, 2nd Embodiment, and each modification is applied. It is explanatory drawing for demonstrating the characteristic of the dichroic mirror of the endoscope apparatus shown in FIG. It is explanatory drawing for demonstrating the characteristic of the dichroic mirror of the endoscope apparatus shown in FIG. It is a figure which shows the other structural example of the endoscope apparatus shown in FIG. It is a figure which shows one structural example of the microscope apparatus to which the illuminating device which concerns on 1st Embodiment, 2nd Embodiment, and each modification is applied. It is explanatory drawing for demonstrating the irradiation range of the irradiation light in an observation site.

Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In this specification and the drawings, constituent elements having substantially the same functional configuration are designated by the same reference numerals, and a duplicate description will be omitted.

The description will be given in the following order.
1. 1. First embodiment 1-1. Configuration of lighting device 1-2. Speckle noise reduction effect 2. Second embodiment 3. Modification 3-1. Modification in which both white light and laser light are combined as divergent light 3-2. 3. Modification in which light source of further wavelength band is added Application example 4-1. About PDD and PDT 4-2. Endoscopic device 4-2-1. Configuration of Endoscope Device 4-2-2. Operation of endoscope device 4-2-3. Another configuration example of the endoscope apparatus 4-3. Microscope device 4-3-1. Configuration of microscope device 4-3-2. Operation of microscope device 5. Supplement

(1. First embodiment)
(1-1. Configuration of lighting device)
The configuration of the lighting device according to the first embodiment of the present disclosure will be described with reference to FIGS. 1 to 5. FIG. 1 is a diagram illustrating a configuration example of the illumination device according to the first embodiment. FIG. 2 is an explanatory diagram for explaining the configuration of the light guide on which the output light from the illumination device shown in FIG. 1 is incident. 3 to 5 are explanatory views for explaining the characteristics of the dichroic mirror of the lighting device shown in FIG.

The illumination device according to the first embodiment and the second embodiment described later can be suitably applied as a light source unit of an observation device such as an endoscope device or a microscope device for observing a surgical site of a patient. Hereinafter, as an example, a case will be described in which the illuminating devices according to the first and second embodiments are applied to an endoscope device except the following (4-3. Microscope device). When the illuminating device according to the first and second embodiments is applied to the endoscope device, the light emitted from the illuminating device is incident on the end portion of the light guide that continues inside the barrel of the endoscope. Therefore, in each of the drawings showing the configuration of the illumination device below, one end of the light guide into which light is incident is also illustrated.

Referring to FIG. 1, the illumination device 10 according to the first embodiment includes a first light source unit 101 that emits white light and a first collimating optical system 103. In addition, the illumination device 10 includes a second light source unit 120 including at least one laser light source that emits light in a predetermined wavelength band, a coupling optical system 105, an optical fiber 107, and a third collimating optical system 109. Further, it further includes a diffusing member 111, a second collimating optical system 113, a dichroic mirror 115, and a condenser optical system 117. Although not shown, the lighting device 10 includes a drive control unit (first light source unit drive control unit 1121 shown in FIG. 10 to be described later, which controls drive of the first light source unit 101 and the second light source unit 120). Corresponding to the second light source unit drive control unit 1123).

The white light emitted from the first light source unit 101 becomes substantially parallel light by passing through the first collimating optical system 103 and enters the dichroic mirror 115. On the other hand, the laser light emitted from the second light source unit 120 passes through the coupling optical system 105, the optical fiber 107, the third collimating optical system 109, the diffusing member 111, and the second collimating optical system 113 in this order. , Becomes substantially parallel light and enters the dichroic mirror 115. The white light and the laser light are combined by the dichroic mirror 115, and the combined light enters the end of the light guide 130 via the condenser optical system 117.

Here, in the illuminating device 10, as the laser light source forming the second light source unit 120, a laser light source capable of emitting light in a wavelength band that can function as excitation light in fluorescence observation depending on the observation purpose can be mounted. .. Then, the illuminating device 10 detects the fluorescence in the operative field by detecting the fluorescence that is excited by the normal observation mode in which the operative field is observed with white light and the light in the predetermined wavelength band (hereinafter, also referred to as narrow band light). It is configured to be switchable between a special observation mode for intensively observing a site where fluorescence is emitted and a normal/special observation mode for simultaneously performing normal observation and special observation (details below (4. Application example) Explained in). The fluorescence observation in the special observation mode and the normal/special observation mode may be to detect the autofluorescence of the excitation light irradiation site or may be caused by various fluorescent reagents (photosensitive agents) introduced into the irradiation site. It may be one that detects the fluorescence of the drug.

In the normal observation mode, the white light generated by combining the white light from the first light source unit 101 and the laser light from the second light source unit 120 is applied to the operative field. As a result, a normal observation image based on white light can be obtained. In the following description, the white light generated by combining the white light from the first light source unit 101 and the laser light from the second light source unit 120 will be referred to as “white light” from the first light source unit 101. For the sake of convenience, it is also referred to as a combined white light in order to distinguish it from the white light. In the normal observation mode, the output of the laser light from the second light source unit 120 is such that the combined white light has a desired hue (for example, a hue similar to the original white light emitted from the first light source unit 101, It is appropriately adjusted so as to obtain a color tone corresponding to any standard light source).

In the special observation mode, white light is not emitted from the first light source unit 101 (that is, the white light source of the first light source unit 101 is turned off), and the laser of the wavelength band corresponding to the observation purpose is emitted from the second light source unit 120. Only the light is emitted (that is, only the laser light source according to the observation purpose is turned on), and thus the narrow-band light is applied to the surgical field. Thereby, a fluorescence observation image based on fluorescence is obtained. In the fluorescence observation image, only a site corresponding to the purpose of observation such as a tumor is shown.

In the normal/special observation mode, similar to the normal observation mode, the combined white light is applied to the operative field. At that time, the output of the laser light from the second light source unit 120 is changed according to the observation purpose. Intensity (that is, intensity suitable for fluorescence observation). As a result, an image in which the normal observation image and the special observation image are superimposed is obtained.

Hereinafter, each component of the lighting device 10 will be described in more detail.

At least one second light source unit 120 is provided in the lighting device 10. The second light source unit 120 is composed of at least one laser light source that emits laser light in a predetermined wavelength band. In the illustrated example, the second light source unit 120 includes a laser light source 121R that emits laser light in the red band (for example, laser light having a center wavelength of about 638 (nm)) and laser light in the green band (for example, center light). A laser light source 121G that emits a laser beam having a wavelength of about 532 (nm) and a laser light source 121B that emits a laser beam in a blue band (for example, a laser beam having a center wavelength of about 450 (nm)) are included. Each laser light source 121R, 121G, 121B is provided with a collimator optical system, and the laser light of each wavelength band is emitted as a parallel light flux.

As the laser light sources 121R, 121G, 121B, various known laser light sources such as a semiconductor laser and a solid-state laser can be used. Alternatively, as the laser light sources 121R, 121G, 121B, a combination of these laser light sources and a wavelength conversion mechanism may be used. In the second light source unit 120, the driving of the laser light sources 121R, 121G, 121B can be controlled independently.

As described above, the second light source unit 120 can be configured by, for example, the laser light sources 121R, 121G, and 121B that emit light in the respective wavelength bands corresponding to the three primary colors of light. By configuring the second light source unit 120 in this way, the color temperature of the combined white light is adjusted by appropriately adjusting the outputs of the laser light sources 121R, 121G, and 121B corresponding to each color, as described later. It will be possible.

However, the first embodiment is not limited to such an example, and the type of the laser light source that constitutes the second light source unit 120 may be appropriately selected according to the purpose of observation, the type of observation target, and the like. For example, if various types of fluorescence observation are performed, the second light source unit 120 is configured to include a laser light source that emits laser light in a wavelength band corresponding to excitation light according to each fluorescence observation method. obtain. For example, when the observation is performed by the ICG (Indocyanine green) fluorescence contrast method, the second light source unit 120 is configured to include at least a laser light source that emits laser light in the near infrared band.

The second light source unit 120 includes a dichroic mirror 122R that reflects light in the wavelength band corresponding to the red laser light from the laser light source 121R, and a dichroic that reflects light in the wavelength band corresponding to the green laser light from the laser light source 121G. The mirror 122G and the dichroic mirror 122B which reflects the light of the wavelength band corresponding to the blue laser light from the laser light source 121B are further included. The dichroic mirrors 122R, 122G, and 122B combine the laser beams, which are parallel light beams emitted from the laser light sources 121R, 121G, and 121B, and combine them into one light beam, which is emitted toward the coupling optical system 105 in the subsequent stage. It

The dichroic mirrors 122R, 122G, 122B are an example of a multiplexing member that multiplexes the laser light from the laser light sources 121R, 121G, 121B, and any other member may be used as the multiplexing member. Good. For example, a dichroic prism may be used as a member for combining the laser light from each of the laser light sources 121R, 121G, and 121B in the case of combining with the wavelength, or a polarized beam in the case of combining with the polarized light. A splitter (PBS: Polarizing Beam Splitter) may be used, and a beam splitter may be used when multiplexing by amplitude.

The coupling optical system 105 is configured by, for example, a condenser lens (collector lens), and optically couples the laser light emitted from the second light source unit 120 to the incident end of the optical fiber 107. In the example shown in FIG. 1, the coupling optical system 105 is illustrated as one convex lens for convenience, but the specific configuration of the coupling optical system 105 is not limited to this example. The coupling optical system 105 may have a function of optically coupling the laser light to the incident end of the optical fiber 107, and may be configured by appropriately combining known optical elements.

The optical fiber 107 guides the laser light emitted from the second light source unit 120 to the third collimating optical system 109 provided in the subsequent stage. Since the light emitted from the optical fiber 107 is a rotationally symmetrical beam, the laser light is guided by the optical fiber 107, so that the luminance distribution in the plane is more uniform.

The type of the optical fiber 107 is not particularly limited, and as the optical fiber 107, a known multimode optical fiber (for example, step index type multimode fiber) can be used. The core diameter of the optical fiber 107 is not particularly limited, and for example, a core diameter of about 1 (mm) may be used.

In the first embodiment, at the incident end of the optical fiber 107, the laser light from the laser light sources 121R, 121G, and 121B is incident on the incident end of the optical fiber 107 so that the incident numerical apertures of the laser light match as much as possible. Is guided. At this time, the focal length of the lens that collimates the laser light emitted from the laser light sources 121R, 121G, and 121B is optimized, and the incident position of the laser light on the coupling optical system 105 (that is, the collector lens) is adjusted. Therefore, the laser light emitted from the emission end of the optical fiber 107 is not a donut-shaped light beam in which the amount of light near the central optical axis of the optical fiber 107 is lower than the amount of light in the peripheral portion, but the center of the optical fiber 107. It is desirable that the light beam be a solid light beam in which the light amount in the vicinity of the optical axis is equal to the light amount in the peripheral portion.

The third collimating optical system 109 is provided after the emission end of the optical fiber 107, and converts the laser light emitted from the optical fiber 107 into a parallel light flux. By converting the laser light into a parallel light flux by the third collimating optical system 109, the diffusion state of the laser light can be easily controlled by the diffusing member 111 provided in the subsequent stage. In the example shown in FIG. 1, the third collimating optical system 109 is illustrated as one convex lens for convenience, but the specific configuration of the third collimating optical system 109 is not limited to this example. The third collimating optical system 109 has only to have a function of converting laser light into a parallel light flux, and may be configured by appropriately combining known optical elements.

The diffusing member 111 is provided in the vicinity of the rear focal position of the third collimating optical system 109, and diffuses the laser light, which is a parallel light flux emitted from the third collimating optical system 109, to generate a secondary light source. Make up. That is, the light emitting end of the diffusing member 111 functions as a secondary light source. Further, the angle of the light emitted from the optical fiber 107 generally varies depending on each laser light, but the divergence angle of these lights is unified by passing through the diffusion member 111. As described above, according to the first embodiment, the diffusion member 111 reduces color unevenness at the time of irradiation, which is expected to occur in, for example, the general existing illumination devices described in Patent Documents 6 to 9 above. Will be done.

The size of the secondary light source generated by the diffusing member 111 can be controlled by the focal length of the third collimating optical system 109. Further, the NA of the emitted light can be controlled by the diffusion angle of the diffusion member 111. Due to the effects of both, it becomes possible to independently control both the size of the focused spot and the incident NA when the light is coupled to the incident end of the light guide 130. It should be noted that the actual range of the vicinity of the rear focus position of the third collimating optical system 109 in which the diffusing member 111 is arranged is not particularly limited, but the range is, for example, It is preferable to include the rear focal position of the third collimating optical system 109, and to set the focal length on the upstream side and the downstream side of the focal point distance to about ±10%.

Note that the specific type of the diffusion member 111 is not particularly limited, and a known diffusion element may be used as the diffusion member 111. Examples of such a diffusing element include, for example, frosted frosted glass, and an opal type diffusing plate or a holographic diffusing plate that utilizes diffusion characteristics by dispersing a light diffusing substance in the glass. The holographic diffusing plate is one in which a holographic pattern is formed on a predetermined substrate, and the diffusing angle of emitted light can be set to an arbitrary angle, and therefore it is particularly preferable to use it as the diffusing member 111.

The laser light emitted from the diffusing member 111 is guided to the second collimating optical system 113. The second collimating optical system 113 converts the light from the diffusing member 111 (that is, the light from the secondary light source) into a parallel light flux and makes it enter the dichroic mirror 115. The dichroic mirror 115 may be a dichroic prism.

Here, the laser light that has passed through the second collimating optical system 113 may not be perfectly parallel light, but may be divergent light that is in a state close to parallel light. In other words, the second collimating optical system 113 and the condenser optical system 117 described later may be finite conjugate instead of infinite conjugate. In the present specification, light that has passed through the collimating optical system and has become parallel light or a state close to parallel light is referred to as substantially parallel light for convenience. That is, substantially parallel light is a concept including parallel light or divergent light. A configuration example of the illumination device 10 in the case where both white light and laser light are combined as divergent light is as follows (3-1. Modification example in which both white light and laser light are combined as divergent light). I will explain again in detail.

At least one first light source unit 101 is provided in the lighting device 10 and emits white light. The white light source that constitutes the first light source unit 101 may be any one that emits white light, and the type thereof is not limited. For example, as the white light source, an arbitrary light source such as a white LED (Light Emitting Diode), a laser excitation phosphor, a xenon lamp, a halogen lamp may be used. In the first embodiment, as an example, a so-called phosphor-type white LED using a phosphor excited by a blue LED is used as the white light source of the first light source unit 101.

The white light emitted from the first light source unit 101 is converted into a parallel light flux by the first collimating optical system 103, and has a different direction from that of the laser light emitted from the diffusing member 111 (in the illustrated example, the optical axes of the two light beams are different from each other). Enters the dichroic mirror 115 from a direction substantially orthogonal to. Note that the white light that has passed through the first collimating optical system 103 does not have to be perfect parallel light. In other words, the first collimating optical system 103 and the condenser optical system 117 described later may be finite conjugate instead of infinite conjugate. That is, the first collimating optical system 103 makes the white light substantially parallel light and makes it enter the dichroic mirror 115.

In the example shown in FIG. 1, the first collimating optical system 103 is illustrated as one convex lens for convenience, but the specific configuration of the first collimating optical system 103 is not limited to this example. The first collimating optical system 103 only needs to have a function of converting white light into substantially parallel light, and may be configured by appropriately combining known optical elements.

The dichroic mirror 115 multiplexes the white light emitted from the first light source unit 101 and the laser light emitted from the second light source unit 120. In the illustrated example, the dichroic mirror 115 is designed to transmit only light in the wavelength band corresponding to the laser light from the second light source unit 120 and reflect light in other wavelength bands.

In the illumination device 10, the diffusing member 111, the second collimating optical system 113, the dichroic mirror 115, and the condenser optical system 117 are arranged in this order in a line. Further, the first light source unit 101 and the first collimating optical system 103 are arranged so that white light is incident on the dichroic mirror 115 from a direction substantially orthogonal to the optical axis of the laser light. Therefore, the laser light emitted from the diffusing member 111 and incident on the dichroic mirror 115 passes through the dichroic mirror 115 and is incident on the condenser optical system 117. Further, of the white light that has entered the dichroic mirror 115, components other than the wavelength band of the laser light are reflected by the dichroic mirror 115 and enter the condenser optical system 117.

In this way, the dichroic mirror 115 attenuates or removes the component of the light in the wavelength band corresponding to the laser light emitted from the second light source unit 120 from the white light emitted from the first light source unit 101, and It has a function of combining the laser light emitted from the second light source unit 120 with the white light in which the light component of the wavelength band corresponding to the laser light is attenuated or removed. That is, the light multiplexed by the dichroic mirror 115 may be white light whose predetermined wavelength band is supplemented by the laser light. Details of the characteristics of the dichroic mirror 115 and the characteristics of the light multiplexed by the dichroic mirror 115 will be described later with reference to FIGS. 3 to 5.

The condenser optical system 117 is composed of, for example, a condenser lens (collector lens), and forms an image of the light combined by the dichroic mirror 115 on the incident end of the light guide 130 at a predetermined paraxial lateral magnification.

Here, the imaging magnification of the second collimating optical system 113 and the condenser optical system 117 ([focal length of the condenser optical system 117]/[focal length of the second collimating optical system 113]) is the size of the secondary light source. And the divergence angle are set to match the core diameter of the light guide 130 and the incident NA. Further, the imaging magnification ([focal length of the condenser optical system 117]/[first collimator optical system 103]) by the first collimating optical system 103 and the condenser optical system 117 depends on the core diameter of the light guide and the incident NA. It is set so that the white light is matched and is efficiently coupled to the incident end of the light guide 130.

FIG. 2 shows a configuration example of the light guide 130. In FIG. 2, the end portion of the light guide 130 is illustrated. As illustrated, the light guide 130 is configured by bundling a plurality of optical fibers each including a fiber core portion and a fiber clad portion. Here, unlike the general configuration, the condenser optical system 117 according to the first embodiment is designed to fill the area of the illumination target (the incident end of the light guide 130 in the first embodiment) as much as possible. It is configured to image the secondary light source. That is, in the first embodiment, in the condenser optical system 117, the size of the image of the secondary light source formed on the incident end of the light guide 130 is substantially the same as the diameter of the incident end of the light guide 130. Thus, the light from the secondary light source may be configured to be focused on the incident end of the light guide 130. As a result, speckle noise of the entire lighting device 10 can be reduced.

Here, it is known that speckle noise depends on the luminance distribution of the light source. For example, when the light source is an ideal point light source, its luminance distribution can be regarded as a δ function, and all points on the object surface irradiated with light from the light source interfere with each other to cause coherence. Becomes higher. That is, the speckle noise becomes large. Such a light source (point light source) is called a coherent light source, and speckle noise becomes large when a coherent light source is used.

On the other hand, if a uniform light source of infinite size is assumed as the light source, its luminance distribution will be uniform, and interference will occur only at the same position on the object plane irradiated with the light from the light source. , Coherence becomes low. That is, speckle noise is reduced. Such a light source having an infinite size is called an incoherent light source, and speckle noise is reduced when the incoherent light source is used.

Since the light source actually mounted on the illumination device 10 is a partially coherent light source spatially located between the coherent light source and the incoherent light source, the apparent size of the light source is large and the luminance distribution of the light source is large. It is considered that the more uniform, the lower the coherence and the less speckle noise.

Here, when the light from the secondary light source is condensed at the incident end of the light guide 130 so that the image of the secondary light source becomes smaller than the diameter of the incident end of the light guide 130, the light guide 130 is Since the constituent optical fibers only partly contribute to the light guide, as a result, when the light emitted from the light guide 130 is applied to the observation site, an apparent light source when observed from the illuminated surface of the observation site. There is a concern that the size will become smaller and the speckle noise will worsen.

On the other hand, when the light from the secondary light source is condensed at the incident end of the light guide 130 so that the image of the secondary light source becomes larger than the diameter of the incident end of the light guide 130, the incident light of the light guide 130 enters. Vignetting of the laser light may occur on the end face, which may reduce the optical coupling efficiency.

Therefore, as described above, the light from the secondary light source is condensed at the incident end of the light guide 130 so that the diameter of the incident end of the light guide 130 and the size of the image of the secondary light source are substantially equal. As a result, speckle noise can be reduced while improving the optical coupling efficiency at the incident end surface of the light guide 130.

Here, for example, the existing general illumination device as shown in Patent Documents 6 to 9 does not apply such a configuration for reducing speckle noise. As described above, according to the lighting device 10 according to the first embodiment, it is possible to obtain an observation image in which speckle noise is further reduced as compared with a general lighting device.

In the example shown in FIG. 1, the condenser optical system 117 is illustrated as one convex lens for convenience, but the concrete configuration of the condenser optical system 117 is not limited to this example. The condenser optical system 117 may have any of the functions described above, and may be configured by appropriately combining known optical elements.

Here, the characteristics of the dichroic mirror 115 and the characteristics of the light multiplexed by the dichroic mirror 115 will be described with reference to FIGS. 3 to 5. FIG. 3A shows an example of a spectrum of white light emitted from the first light source unit 101. FIG. 3B shows an example of the reflection characteristic of the dichroic mirror 115.

Referring to FIG. 3B, the dichroic mirror 115 reflects most of the wavelength band of white light and transmits light in the wavelength band corresponding to the laser light emitted from the second light source unit 120. It has the property of In the illustrated example, the dichroic mirror 115 includes light in a wavelength band of a predetermined width including the center wavelength of the red laser light of about 638 (nm) and about 532 (nm) of the center wavelength of the green laser light. It is designed to transmit light in a wavelength band of a predetermined width and light in a wavelength band of a predetermined width including about 450 (nm) which is the central wavelength of blue laser light.

FIG. 3C shows an example of a spectrum of light after the white light emitted from the first light source unit 101 has passed through the dichroic mirror 115. As shown in FIG. 3C, the white light that has passed through the dichroic mirror 115 has the components in the wavelength band corresponding to the laser light emitted from the second light source unit 120 attenuated. .. As described above, since only the wavelength band corresponding to the laser light is attenuated by the dichroic mirror 115, it is possible to minimize the loss when the white light and the laser light are combined. Further, when the white light is substantially parallel light and has a wide incident angle, a wavelength shift occurs due to the incident angle dependence of the dichroic mirror 115, and the attenuated wavelength band is also shifted. Therefore, after the light guide 130 is emitted. , There is a tendency that the spectrum is made more uniform than in FIG.

The characteristic of the dichroic mirror 115 shown in FIG. 3 is an example, and the first embodiment is not limited to such an example. The characteristics of the dichroic mirror 115 can be appropriately set according to the characteristics of the laser light source used as the second light source unit 120. For example, when the observation by the above-described ICG fluorescence contrast method is performed, the second light source unit 120 receives a laser beam in the near infrared band (for example, a laser beam having a central wavelength of about 808 (nm)). Since it can be used, the dichroic mirror 115 having a characteristic of transmitting light in a range corresponding to the wavelength band of the laser light is used.

FIG. 4 shows an example of the transmission characteristics of the dichroic mirror 115. As described with reference to FIG. 3B, the dichroic mirror 115 transmits the light in the wavelength band corresponding to the laser light emitted from the second light source unit 120, and emits the light from the first light source unit 101. It can be seen that most of the wavelength band of the white light that is reflected is reflected. In the illustrated example, the dichroic mirror 115 is set to transmit about 90% of the light in the corresponding wavelength band in order to improve the utilization efficiency of the laser light.

FIG. 5 shows an example of a spectrum of light after the white light emitted from the first light source unit 101 and the laser light emitted from the second light source unit 120 are combined by the dichroic mirror 115. There is. In the illustrated example, a spectrum when white light is combined with red laser light, green laser light, and blue laser light is shown. As described above, in the first embodiment, the white light and the laser light can be combined, and so to speak, new white light (that is, combined white light) can be generated. In the first embodiment, the combined white light is applied to the operative field in the normal observation mode and the normal/special observation mode. In the special observation mode, the first light source unit 101 is not driven, but only the second light source unit 120 is driven, and the laser light in the wavelength band corresponding to the excitation light when performing fluorescence observation is incident on the surgical field. It is irradiated against.

Here, for example, in the existing general illumination devices shown in Patent Documents 6, 8 and 9 described above, white light and laser light are guided on the same optical axis by the multiplexing member, but at this time, white light and laser light are emitted. By selectively controlling the drive of the light source and laser light source, and by appropriately controlling the withdrawal of the filter from the optical path and the placement of the filter in the optical path, either white light or laser light is selectively applied to the operative field. To be done. That is, in the techniques described in Patent Documents 6, 8, and 9, in the normal observation mode, the white light from the white light source is directly applied to the operative field. Further, in the technique described in Patent Document 7, white light generated by combining the white light and the laser light by the combining member is applied to the operative field, but the combining member is a part thereof. Is composed of a transmissive part that transmits the components of the entire wavelength band of the white light, and as a result, the white light from the white light source that has passed through the transmissive part is directly irradiated to the surgical field. It will be.

As described above, in the existing general illumination devices exemplified in Patent Documents 6 to 9 described above, in the normal observation mode, white light from a white light source such as a halogen lamp or a white LED is directly applied to the operative field. Can be illuminated. Therefore, the spectrum of white light emitted to the operative field is basically fixed according to the type of white light source, even if it can be adjusted to some extent using various filters. It has been difficult to control the spectrum of the white light emitted in detail.

On the other hand, according to the first embodiment, as described above, the white light emitted from the first light source unit 101 and the laser light emitted from the second light source unit 120 are combined and generated. White light may be illuminated on the operative field in the normal observation mode and the normal/special observation mode. Further, the second light source unit 120 can be configured by, for example, laser light sources 121R, 121G, and 121B that emit light in each wavelength band corresponding to the three primary colors of light. According to this configuration, it is possible to control the spectrum of the combined white light and adjust the color temperature by appropriately adjusting the mixing ratio of the laser light emitted from the second light source unit 120. As described above, according to the first embodiment, it is possible to adjust the color temperature on the light source side instead of adjusting the color temperature on a stage subsequent to the lighting device by using the filter or the like.

At this time, the mixing ratio of the laser light emitted from the second light source unit 120 is adjusted, for example, by controlling the drive current of each of the laser light sources 121R, 121G, and 121B to control the output of the laser light. Alternatively, it may be controlled by adjusting the transmittance of light in the wavelength band corresponding to each laser light in the dichroic mirror 115.

As an example, Table 1 below shows a setting example of the output of each light source for realizing a predetermined color temperature in the combined white light. For example, when it is desired to realize white light by the D65 standard light source (x=0.313, y=0.329) by the illumination device 10, the outputs of the white light source and the laser light source are set as shown in column (a) of Table 1. do it. Further, for example, when it is desired to realize white light by the D50 regular light source (x=0.346, y=0.359) by the lighting device 10, the outputs of the white light source and the laser light source are as shown in the column of Table 1(b). You can set it to. The settings shown in Table 1 below are merely examples, and it goes without saying that the color temperature of white light by various other light sources can be realized by appropriately adjusting the outputs of the white light source and the laser light source.

The configuration of the lighting device 10 according to the first embodiment has been described above with reference to FIGS. 1 to 5. As described above, according to the first embodiment, the diffusion member 111 is provided on the optical path of the laser light, so that the divergence angles of the plurality of laser lights emitted from the second light source unit 120 are unified. Therefore, color unevenness at the time of irradiation of the output light from the illumination device 10 is reduced. In addition, the condenser optical system 117 is configured to image the light from the secondary light source on the incident end of the light guide 130 so as to fill the area of the incident end of the light guide 130 as much as possible. The speckle noise as a whole can be reduced. Moreover, the color temperature of the combined white light can be adjusted by adjusting the mixing ratio of the laser light in the second light source unit 120. Therefore, according to the first embodiment, in the observation using the white light (that is, the observation in the normal observation mode or the normal/special observation mode), the more uniform and high-quality white light can be used as the irradiation light. It becomes possible to obtain a higher quality observation image.

Further, in the illumination device 10 according to the first embodiment, as described above, by appropriately controlling the driving of the first light source unit 101 and the second light source unit 120, the normal observation mode and the special observation mode are set. , It is possible to switch between the normal/special observation mode. As described above, according to the first embodiment, it is possible to switch the wavelength band of the irradiation light and obtain a higher quality observation image at the same time.

Here, in the configuration example described above, in order to increase the utilization efficiency of the laser light emitted from the second light source unit 120, as shown in FIG. 4, the transmittance of light corresponding to the wavelength band of the laser light is increased. The performance of the dichroic mirror 115 was adjusted so as to be about 90 (%). However, the first embodiment is not limited to such an example. For example, when the laser power has a margin, the light transmittance of the dichroic mirror 115 corresponding to the wavelength band of the laser light may be set to another value such as 50 (%). Further, in the dichroic mirror 115, the light transmittances corresponding to the wavelength bands of the laser light in the respective wavelength bands may be set to different values.

Further, in the configuration example described above, the white light reflected by the dichroic mirror 115 and the laser light transmitted through the dichroic mirror 115 are multiplexed, but the first embodiment is not limited to this example. By setting the reflection characteristic and the transmission characteristic of the dichroic mirror 115 to be opposite to the above-mentioned characteristics, the white light transmitted through the dichroic mirror 115 and the laser light reflected by the dichroic mirror 115 are combined. The illumination device 10 may be configured such that the combined and combined light enters the light guide 130 via the condenser optical system 117.

The configuration illustrated in FIG. 1 is merely an example of the configuration of the lighting device 10, and the configuration of the lighting device 10 is not limited to this example. The lighting device 10 may further include various optical elements that can be mounted on a general existing lighting device. For example, when a xenon lamp is used as the white light source of the first light source unit 101, the near-infrared band light that can contribute to the heat generation of the living body at the time of irradiation is attenuated or removed in the subsequent stage of the first light source unit 101. A filter or the like may be provided. Alternatively, a filter or the like for attenuating or removing light in the near infrared band may be provided in front of the image sensor used for observing the subject. Alternatively, instead of providing the filter, the function of the filter may be realized by the dichroic mirror 115. That is, by adjusting the reflection characteristic or the transmission characteristic of the dichroic mirror 115, the near-infrared band component may be attenuated or removed from the white light emitted from the first light source unit 101 at the time of multiplexing. Good.

(1-2. Speckle noise reduction effect)
An experimental device having the same configuration as the illumination device 10 according to the first embodiment is created, and the white light emitted from the first light source unit 101 and the second light source unit 120 are emitted using the experimental device. The speckle noise when the observation target is irradiated with white light generated by being combined with the generated laser light is investigated. Results are shown in FIG. FIG. 6 is a diagram showing the effect of reducing speckle noise by the lighting device 10 according to the first embodiment.

The horizontal axis of the graph shown in FIG. 6A indicates the ratio (L_LED/L_Laser) between the output (L_LED) of the first light source unit 101 and the output (L_Laser) of the second light source unit 120. .. L_LED is the total output of the white light source (white LED) which comprises the 1st light source part 101, and L_Laser is the total output of the laser light sources 121R, 121G, and 121B which comprise the 2nd light source part 120. Further, the vertical axis of the graph shown in FIG. 6A indicates the speckle contrast ratio (SCR) corresponding to the speckle amount in the observation image observed using the combined white light. On the other hand, FIG. 6B shows an example of an observation image observed using the combined white light.

From FIG. 6, the speckle noise amount changes according to the output ratio (L_LED/L_Laser) of the white light source and the laser light source, and the output ratio is 1, that is, the output of the white light source and the output of the laser light source. It can be seen that the speckle noise amount is further reduced when the values are almost equal. From the result, it was confirmed that according to the first embodiment, the speckle noise can be further reduced by adjusting the output ratio of the white light source and the laser light source to be combined.

(2. Second embodiment)
The configuration of the lighting device according to the second embodiment of the present disclosure will be described with reference to FIG. 7. FIG. 7 is a diagram showing a configuration example of the illumination device according to the second embodiment. Here, the illumination device according to the second embodiment shown in FIG. 7 is the same as the illumination device 10 according to the first embodiment shown in FIG. 1 described above, except for the coupling optical system 105, the optical fiber 107, and the third collimating optics. The system 109 corresponds to the omitted one. Therefore, in the following description of the second embodiment, the detailed description of the items overlapping with the first embodiment will be omitted, and the items different from the first embodiment will be mainly described.

Referring to FIG. 7, the illumination device 20 according to the second embodiment emits white light, a first light source unit 101, a first collimating optical system 103, and at least emits light in a predetermined wavelength band. It has the 2nd light source part 120 which consists of one laser light source, the diffusing member 111, the 2nd collimating optical system 113, the dichroic mirror 115, and the condenser optical system 117. Here, since the configuration and function of each of these members are the same as the configuration and function of each member shown in FIG. 1, detailed description of each member will be omitted.

In the illuminating device 20, like the illuminating device 10 according to the first exemplary embodiment, the white light emitted from the first light source unit 101 is converted into substantially parallel light by the first collimating optical system 103, and the dichroic mirror is used. It is incident on 115. On the other hand, in the illumination device 20, unlike the illumination device 10 according to the first embodiment, the laser light emitted from the second light source unit 120 directly enters the diffusion member 111 and is diffused (that is, the laser light is emitted). The laser light from the secondary light source) is converted into substantially parallel light by the second collimating optical system 113 and is incident on the dichroic mirror 115. Even with a simpler configuration such as the illumination device 20, the same effect of improving the quality of the combined white light as in the first embodiment can be obtained, and the observation image can be of higher quality. Can be

The configuration of the lighting device 20 according to the second embodiment has been described above with reference to FIG. 7. As described above, according to the second embodiment, the same effect as that of the first embodiment can be obtained with a simpler configuration. Therefore, in addition to the effect obtained in the first embodiment, it is possible to realize the downsizing of the lighting device 20 and the reduction of the manufacturing cost.

However, as described in (1-1. Configuration of the illuminating device), the laser light is guided by the optical fiber 107, so that the luminance distribution of the laser light emitted from the optical fiber 107 is more uniform. It has the effect of being converted. Therefore, in order to further improve the quality of the output light, it is preferable to provide the optical fiber 107 like the illumination device 10 according to the first embodiment. Whether the configuration of the illumination device 10 according to the first embodiment or the configuration of the illumination device 20 according to the second embodiment is adopted depends on the quality of output light required for the application and the manufacturing of the device. It may be appropriately determined in consideration of costs and the like.

(3. Modified example)
Some modifications of the first and second embodiments described above will be described. In the following description of each modified example, as an example, a case where the configuration corresponding to each modified example is applied to the lighting device 10 according to the first embodiment illustrated in FIG. 1 will be described. The configurations corresponding to the modified examples can be similarly applied to the illumination device 20 according to the second embodiment.

(3-1. Modification example in which both white light and laser light are combined as divergent light)
With reference to FIG. 8, a configuration of an illumination device in a modified example in which both white light and laser light are combined as divergent light will be described. FIG. 8 is a diagram showing a configuration example of a lighting device in the case where both white light and laser light are combined as divergent light.

Here, the illumination device according to the present modification shown in FIG. 8 is the same as the illumination device 10 according to the first embodiment shown in FIG. 1 described above, except that the first collimating optical system 103, the second collimating optical system 113, and This corresponds to the optical characteristics of the condenser optical system 117 changed. Therefore, in the following description of the present modified example, detailed description of matters overlapping with those of the first embodiment will be omitted, and matters different from those of the first embodiment will be mainly described.

Referring to FIG. 8, the illumination device 30 according to the present modified example includes a first light source unit 101 that emits white light, a first collimating optical system 103a, and at least one light that emits light in a predetermined wavelength band. A second light source unit 120 including a laser light source, a coupling optical system 105, an optical fiber 107, a third collimating optical system 109, a diffusing member 111, a second collimating optical system 113a, and a dichroic mirror 115. , And a condenser optical system 117a. Here, the configurations and functions of the first light source unit 101, the second light source unit 120, the coupling optical system 105, the optical fiber 107, the third collimating optical system 109, the diffusing member 111, and the dichroic mirror 115 are shown in FIG. Since the configurations and functions of these members shown are the same, detailed description of each of these members will be omitted.

In the present modification, the first collimating optical system 103a causes the white light emitted from the first light source unit 101 to enter the dichroic mirror 115 as divergent light, not as perfect parallel light. The second collimating optical system 113a perfectly matches the laser light emitted from the second light source unit 120 and diffused by the diffusing member 111 (that is, the laser light from the secondary light source) with the white light. Instead, it is incident on the dichroic mirror 115 as divergent light. In the dichroic mirror 115, the white light and the laser light, both of which are divergent light, are combined, and the combined light is combined with the end of the light guide 130 by the condenser optical system 117a. At this time, similarly to the first embodiment, the condenser optical system 117a uses the light from the secondary light source so that the light from the secondary light source fills the area of the incident end of the light guide 130 as much as possible. It is configured to collect light on the incident end face of 130.

Here, in general, since it is necessary to increase the light emitting area of an LED in order to obtain a high output, the light emitted from the LED is strongly isotropically emitted, and a collimating lens is used. Even if it is, it is difficult to make a perfect parallel light. Therefore, also in the first embodiment, when a white LED is used as the first light source unit 101, the white light from the first light source unit 101 is converted into perfect parallel light by the first collimating optical system 103. Difficult to do. In this modification, the laser light is also divergent in accordance with the white light in this way, in response to the case where it is difficult to convert the white light into perfect parallel light, and both are combined as divergent light. It is something that surfs. In that sense, it can be said that the lighting device 30 shown in FIG. 8 more strictly illustrates the configuration of the lighting device 10 when the white LED is used as the first light source unit 101 in the first embodiment. ..

In the present modification, as described above, the white light and the laser light, both of which are divergent lights, are combined, and the combined light is coupled to the end of the light guide 130 by the condenser optical system 117a. That is, the first collimating optical system 103a and the condenser optical system 117a, and the second collimating optical system 113a and the condenser optical system 117a are both finite conjugates. The condenser optical system 117a has an optical characteristic that the combined light is appropriately coupled to the incident end face of the light guide 130 according to the optical characteristic of the first collimating optical system 103a and the second collimating optical system 113a. It is designed appropriately. As a result, in the illumination device 30 according to the present modification, the same effect of improving the quality of the combined white light as in the first embodiment can be obtained, and the observation image can have a higher quality. ..

Note that, in the example shown in FIG. 8, the first collimating optical system 103a, the second collimating optical system 113a, and the condenser optical system 117a are each illustrated by a single convex lens for convenience. The specific configuration is not limited to this example. The first collimating optical system 103a, the second collimating optical system 113a, and the condenser optical system 117a may each have the above-described functions, and may be configured by appropriately combining known optical elements.

The configuration of the illumination device 30 in the modified example in which both white light and laser light are combined as divergent light has been described above. As described above, for example, even when the white LED is used as the first light source unit 101 and it is difficult to convert the white light into the perfect parallel light, as in the present modification, the first By appropriately adjusting the optical characteristics of the collimating optical system 103a, the second collimating optical system 113a, and the condenser optical system 117a, it is possible to configure the illuminating device 30 having the same effect as that of the first embodiment. ..

(3-2. Modification in which light source of further wavelength band is added)
In the first and second embodiments described above, the case where the white light, the red laser light, the green laser light, and the blue laser light are combined is described. With this configuration, in the special observation mode, red laser light, green laser light, blue laser light, or a mixture of any of these laser lights is used as irradiation light. However, depending on the purpose of observation in the special observation mode, there may be a desire to use light in another wavelength band different from these laser lights as irradiation light. Here, as a modified example of the first and second embodiments, a configuration of the lighting device in the case where a light source of a further wavelength band is added to the lighting device 10 according to the first embodiment will be described. To do.

With reference to FIG. 9, a configuration of a lighting device in a modified example in which a light source in a further wavelength band is added will be described. FIG. 9 is a diagram showing a configuration example of a lighting device when a light source of a further wavelength band is added.

Here, the lighting device according to the present modification shown in FIG. 9 is obtained by adding a third light source unit 119 described later to the lighting device 10 according to the first embodiment shown in FIG. 1 described above. Correspond. Therefore, in the following description of the present modified example, detailed description of matters overlapping with those of the first embodiment will be omitted, and matters different from those of the first embodiment will be mainly described.

Referring to FIG. 9, the illumination device 40 according to the present modification example includes a first light source unit 101 that emits white light, a first collimating optical system 103, and at least one light source that emits light in a predetermined wavelength band. A second light source unit 120 including a laser light source, a coupling optical system 105, an optical fiber 107, a third collimating optical system 109, a diffusing member 111, a second collimating optical system 113, and a dichroic mirror 115. It has a condenser optical system 117, a third light source unit 119, and a dichroic mirror 125. Here, the configuration and function of each member other than the third light source unit 119 and the dichroic mirror 125 are the same as the configuration and function of these members shown in FIG. 1, and thus a detailed description of each of these members will be given. Is omitted. Further, the dichroic mirror 125 is also referred to as a second dichroic mirror 125 in order to distinguish it from the dichroic mirror 115 for multiplexing white light and laser light.

As shown in the figure, in the illumination device 40 according to the present modification, the second dichroic mirror 125 is provided in the optical path from the first light source unit 101 to the dichroic mirror 115. Then, the third light source unit 119 is provided so that the emitted light enters the second dichroic mirror 125 in a direction substantially perpendicular to the optical path from the first light source unit 101 toward the dichroic mirror 115.

The third light source unit 119 emits light in a wavelength band different from that of the laser light emitted from the second light source unit 120. Here, as an example, a case will be described in which the third light source unit 119 is configured by an LED that emits ultraviolet light having a center wavelength of 410 (nm). Although not shown in the figure for simplification, a collimator lens or the like that makes the light emitted from the third light source unit 119 into substantially parallel light and enters the second dichroic mirror 125 is a third light source unit 119. It is provided in the latter stage.

The second dichroic mirror 125 has a characteristic of transmitting white light emitted from the first light source unit 101 and reflecting ultraviolet light having a wavelength near 410 (nm) emitted from the third light source unit 119. .. As a result, the second dichroic mirror 125 multiplexes the white light and the ultraviolet light, and the combined light is incident on the dichroic mirror 115.

The dichroic mirror 115 has a characteristic of transmitting light in the wavelength band corresponding to the laser light from the second light source unit 120, as in the first embodiment. Therefore, in the present modification, the light obtained by attenuating or removing the component of the wavelength band corresponding to the laser light from the light obtained by combining the white light and the ultraviolet light is reflected by the dichroic mirror 115, and the light is converted into the laser light. Will be combined. As described above, in the lighting device 40 according to the present modification, it is possible to output the light in which the ultraviolet light is superimposed on the output light of the lighting device 10 according to the first embodiment as the combined white light. Become.

The configuration of the illumination device 40 in the modification example in which the light source in the further wavelength band is added has been described above with reference to FIG. 9. As described above, according to the present modification, the light obtained by superimposing the light emitted from the third light source unit 119 on the output light of the illumination device 10 according to the first embodiment is the combined white light. Can be output as The combined white light is generated as in the first embodiment except that the light emitted from the third light source unit 119 is added. Therefore, in the lighting device 40 according to the present modification, the first embodiment is performed. Similar to the form, the effect of improving the quality of the combined white light used as the irradiation light in the normal observation mode or the normal/special observation mode can be obtained, and the observation image can be made higher in quality. On the other hand, in the special observation mode, by operating only the third light source unit 119 according to the purpose of observation, it is possible to irradiate the surgical site with ultraviolet light. As described above, in the present modification, it is possible to more appropriately output light in the wavelength band according to the observation purpose while realizing the effects obtained in the first embodiment, and thus, it is possible to support more diverse applications. The resulting lighting device 40 is realized.

Here, in the case of adding a light source of a further wavelength band, a configuration in which a laser light source is added to the second light source unit 120 can be considered. For example, in the above example, by adding a laser light source that emits laser light in a wavelength band corresponding to ultraviolet light to the second light source unit 120, output light similar to that of the lighting device 40 can be obtained. .. However, in general, the laser light source is more expensive than the LED, and the configuration tends to be large. By configuring the third light source unit 119 with LEDs as in the illustrated configuration, it is possible to realize the lighting device 40 at a lower cost and with a smaller size.

The reflection characteristic and the transmission characteristic of the second dichroic mirror 125 may be set to be opposite to the above-mentioned characteristics. In this case, the ultraviolet light transmitted through the second dichroic mirror 125 is combined with the white light reflected by the dichroic mirror 125, and the combined light is incident on the dichroic mirror 115. Further, similarly to the first embodiment, the reflection characteristic and the transmission characteristic of the dichroic mirror 115 may be set to be opposite to the above-mentioned characteristics.

In addition, the second icroic mirror 125 is an example of a combining member for combining white light and ultraviolet light, and the combination of the white light and the ultraviolet light is, for example, a polarization beam splitter or the like. It may be performed by a combination member of a kind.

Further, the configurations according to the first embodiment, the second embodiment, and the modified examples described above may be combined with each other within a possible range. Here, as described in the above (3-1. Modification in which both white light and laser light are combined as divergent light), in general, for the light emitted from the LED, a collimator lens may be used. It is difficult to make perfect parallel light. Therefore, in the configuration example shown in FIG. 9, when LEDs are used as the first light source unit 101 and/or the third light source unit 119, the emitted light may be divergent light instead of perfect parallel light. .. Therefore, when LEDs are used as the first light source unit 101 and/or the third light source unit 119 in the configuration example shown in FIG. 9, in combination with the configuration example shown in FIG. It is preferable that the optical characteristics of the first collimating optical system 103, the second collimating optical system 113, and the condenser optical system 117 are appropriately adjusted.

(4. Application example)
An application example of the lighting devices 10, 20, 30, and 40 according to the first embodiment, the second embodiment, and each modification described above will be described. Here, as one application example, the illumination devices 10, 20, 30, and 40 are applied to an observation device capable of performing photodynamic diagnosis (PDD) and photodynamic therapy (PDT). The case will be described.

Below, PDD and PDT are demonstrated first. Then, a general existing observation apparatus capable of executing PDD and PDT will be described, and problems in these general observation apparatuses will be described. Next, a configuration example and an operation example of the observation device to which the illumination devices 10, 20, 30, and 40 are applied will be described.

(4-1. About PDD and PDT)
PDD and PDT are less invasive tumor diagnosis and treatment methods using photosensitizers, and are applied to the diagnosis and treatment of early lung cancer, early esophageal cancer, gastric cancer, early cervical cancer, malignant brain tumor, etc. ..

PDD utilizes the property of a photosensitive drug that emits fluorescence when excited by excitation light in a predetermined wavelength band. Since the photosensitizer administered to the patient has the property of selectively accumulating in the tumor, the tumor site is diagnosed by irradiating the operating field with excitation light and detecting the fluorescence emitted from the photosensitizer. can do.

PDT utilizes the property of a photosensitizing agent that generates active oxygen upon irradiation with excitation light in a predetermined wavelength band. As described above, since the photosensitizing drug administered to the patient has the property of selectively accumulating in the tumor, irradiation of the surgical field with excitation light mainly generates active oxygen at the tumor site. The tumor site can be treated by denaturing and dying the tumor site. The excitation light irradiation for performing PDD and PDT corresponds to the operation of the illumination devices 10, 20, 30, 40 in the special observation mode in the above-described embodiment.

When the surgical field is irradiated with only the excitation light, the tumor site can be observed, but the normal state of the entire surgical field cannot be observed. Therefore, generally, an observation apparatus capable of performing PDD and PDT has a function of switching or simultaneously performing irradiation of white light for performing normal observation and irradiation of excitation light for performing PDD and PDT. There is something installed.

For example, Japanese Patent Laid-Open No. 2006-000157 (hereinafter referred to as Reference Document 1) describes an observation in which irradiation with white light for normal observation and irradiation with laser light (excitation light) for fluorescence observation can be switched. A light source device for a device (endoscopic device) is disclosed. In the technique described in Reference Document 1, the white light and the excitation light are on the same optical axis by a dichroic mirror having a characteristic of transmitting the white light emitted from the white light source and reflecting most of the excitation light from the laser light source. Be guided. Then, by appropriately controlling the movement of the shielding plate provided in the subsequent stage of the white light source and the driving of the laser light source, white light or excitation light is incident on the end portion of the light guide. As described above, the light source device described in Reference Document 1 is configured to be capable of switching between the normal observation mode and the special observation mode. Note that Reference Document 1 is the same document as Patent Document 9 described above.

For example, in JP-A-2006-296516 (hereinafter referred to as Reference Document 2), a white light source for normal observation is provided near an inlet of observation light (that is, fluorescence) during fluorescence observation. An observation device (microscope device) capable of bright-field observing a peripheral region of a lesion that emits fluorescence is disclosed. In the technique described in Reference Document 2, as a light source provided at the inlet of observation light, a wavelength region corresponding to fluorescence emitted from a lesion has a relatively lower intensity than other wavelength bands, or a filter is used. By using a white light source that emits cut visible light, it is possible to simultaneously observe the lesion area that emits fluorescence and the surrounding area. As described above, the observation device described in Reference Document 2 is configured to allow observation of the operative field in the normal/special observation mode.

For example, in Japanese Unexamined Patent Application Publication No. 2009-226067 (hereinafter referred to as Reference Document 3), a white light source and a plurality of filters for extracting light of a predetermined wavelength band from white light from the white light source are in-plane. And a rotation filter provided in different areas of the observation device. In the technique described in Reference Document 3, a rotating filter extracts, from white light, light corresponding to a wavelength band of excitation light corresponding to the first photosensitizing agent, and white light to second light. A second filter that extracts light corresponding to the wavelength band of the excitation light corresponding to the sensitive drug and a third filter that extracts light corresponding to the wavelength band of visible light from white light are provided. Then, the rotation angle of the rotary filter is controlled and the filter through which the white light passes is switched, whereby the irradiation of the excitation light and the irradiation of the visible light are switched. As described above, the observation device described in Reference Document 3 is configured to be capable of switching between the normal observation mode and the special observation mode.

However, the technique described in Reference Document 1 does not assume a method of use in which white light and excitation light are emitted simultaneously (that is, a method of use corresponding to a normal/special observation mode), and white light and excitation light Irradiation is time-shared. Therefore, it is necessary to provide the shield plate that shields the white light and the drive mechanism for the shield plate as described above, and the device may be complicated and large. Also, due to the configuration of the device, the white light that enters the light guide via the dichroic mirror is white light in which the wavelength component corresponding to the excitation light has been cut or attenuated, and has a different hue from the original white light. , There is a possibility that a high quality observation image may not be obtained during normal observation. Further, the light source device described in Reference Document 1 is provided with a photodetector that detects the intensity of the excitation light in order to adjust the output of the laser light source, but white light also reaches the photodetector. Since it is configured to obtain, the detection value of the photodetector is one in which the intensity of excitation light and the intensity of white light are superimposed, the output of the laser light source is not properly controlled, and high quality is observed during fluorescence observation. There is a possibility that a good observation image may not be obtained.

Further, in the technique described in Reference Document 2, the optical path of white light for normal observation and the optical path of excitation light for fluorescence observation are different from each other, and the irradiation angles of these lights with respect to the operative field are also different from each other. Therefore, the shadow appearing in the observed image due to the shape of the operative field may change between normal observation and fluorescence observation. Therefore, there is a possibility that a shadow may be generated at the site where no shadow is seen during normal observation during fluorescence observation. The part that is shaded during fluorescence observation is the part where the excitation light cannot reach, so the part that was aimed at fluorescence observation during normal observation should be observed when actually attempting fluorescence observation. This is not possible, and it may be difficult to perform appropriate observation according to the user's request.

Further, in the technique described in Reference Document 3, as in the technique described in Reference Document 1, a method of use in which white light and excitation light are simultaneously emitted (that is, a method of use corresponding to the normal/special observation mode) is assumed. However, the white light and the excitation light are emitted in a time division manner. In the technique described in Reference Document 3, as described above, the irradiation of the white light or the excitation light in time division is realized by using the rotary filter, but the rotary filter and the drive mechanism of the rotary filter are required. Therefore, the device may be complicated and large.

As described above, in the general existing technology, while performing normal observation and/or fluorescence observation with a simpler configuration, as for the configuration capable of obtaining a higher quality observation image in normal observation and/or fluorescence observation, , Was not considered enough. On the other hand, according to the present disclosure, by applying the illumination devices 10, 20, 30, and 40 according to the first embodiment, the second embodiment, and the modified examples described above to the observation device, normal observation and It is possible to achieve both the execution of fluorescence observation with a simpler configuration and the acquisition of higher quality observation images in normal observation and/or fluorescence observation. Hereinafter, a configuration example of the observation device to which the illumination devices 10, 20, 30, 40 are applied will be described in detail.

(4-2. Endoscopic device)
(4-2-1. Configuration of Endoscopic Device)
With reference to FIGS. 10 to 12, the configuration of the illumination device 10, 20, 30, 40 when applied to the endoscope device will be described. FIG. 10: is a figure which shows one structural example of the endoscope apparatus to which the illuminating device 10, 20, 30, 40 which concerns on 1st Embodiment, 2nd Embodiment, and each modification is applied. 11 and 12 are explanatory diagrams for explaining the characteristics of the dichroic mirror of the endoscope device shown in FIG. 10.

Note that, in the following description, as an example, a case will be described in which a configuration corresponding to the illumination device 20 according to the second embodiment is mounted on the endoscope device. However, this application example is not limited to such an example, and configurations corresponding to the other illumination devices 10, 30, and 40 may be mounted on the endoscope device.

Referring to FIG. 10, the endoscope device 1 includes a lighting device 1100, an endoscope section 1200, an image processing device 1300, and a display device 1400. In addition, in FIG. 10, the observation site 1500 to which the output light from the illumination device 1100 is irradiated is also schematically illustrated.

(Lighting device 1100)
The illumination device 1100 generates white light for normal observation (combined white light) and excitation light for fluorescence observation. The combined white light and/or excitation light generated by the illumination device 1100 enters the light guide 130, is guided by the light guide 130 into a lens barrel 1210 described below, and is observed from the tip of the lens barrel 1210 to an observation site 1500. Is irradiated against.

Here, the lighting device 1100 corresponds to the lighting device 20 according to the second embodiment described above. However, when the endoscope device 1 is mounted, some members are added.

Specifically, the illuminating device 1100 includes a first light source unit 101 that emits white light, a first collimating optical system 103, and a second light source that emits light in a predetermined wavelength band. Light source section 120b, diffusing member 111, second collimating optical system 113, dichroic mirror 115b, condenser optical system 117, laser line filter 1101, half mirror 1103, photodetector 1105, and half mirror. 1107, a photodetector 1109, and a control unit 1120.

As described above, in the lighting device 1100, the laser line filter 1101, the half mirror 1103, the photodetector 1105, the half mirror 1107, and the photodetector 1109 are added to the lighting device 20 according to the second embodiment. , The second light source unit 120 and the dichroic mirror 115 have changed optical characteristics. The configurations and functions of the other members are the same as the configurations and functions of these members shown in FIG. 7, and thus detailed description of each of these members is omitted. The control unit 1120 corresponds to a control unit, which is omitted in FIG. 7, for controlling the driving of the first light source unit 101 and the second light source unit 120b.

Here, the second light source unit 120b corresponds to the second light source unit 120 of the illuminating device 20 in which the wavelength band of the laser light that can be emitted is changed, and the dichroic mirror 115b corresponds to the illuminating device 20. This corresponds to the dichroic mirror 115 of which the reflection characteristic and the transmission characteristic are changed. The other configurations and functions of the second light source unit 120b and the dichroic mirror 115b are similar to the configurations and functions of these members in the lighting device 20, and therefore the second light source unit 120b and the dichroic mirror 115b have already been described. Detailed description of the items that overlap with the items that have been performed will be omitted.

10 shows the second light source unit 120b in a simplified manner, the second light source unit 120b is similar to the second light source unit 120 shown in FIG. 7 and includes at least one laser light source. It is configured. However, as at least one of the laser light sources constituting the second light source unit 120b, one capable of emitting laser light in the wavelength band used as excitation light in the PDD and PDT is mounted.

As illustrated, the laser line filter 1101 is provided, for example, between the third collimating optical system 109 and the diffusing member 111. The laser line filter 1101 is a so-called bandpass filter (BPF) that transmits only light outside the predetermined wavelength band. The laser line filter 1101 is set so as to remove a spectrum other than the laser oscillation wavelength (for example, a spontaneous emission light component of the laser light source forming the second light source unit 120). By passing the laser light emitted from the second light source unit 120b through the laser line filter 1101, an extra wavelength band component that may be noise in the observation image is removed from the laser light, and the wavelength band corresponding to the excitation light is removed. Only the component of will be extracted from the laser light.

A half mirror 1103 is provided after the laser line filter 1101. Part of the laser light demultiplexed by the half mirror 1103 enters the photodetector 1105. The photodetector 1105 has a function of detecting the intensity of light, and the detected value is provided to the second light source unit drive control unit 1123 of the control unit 1120 described below. The second light source unit drive control unit 1123 drives each laser light source of the second light source unit 120b based on the detected value so that, for example, the total output of the laser light from the second light source unit 120b becomes constant. To control. In this way, by providing the configuration for monitoring the output of the laser light emitted from the second light source unit 120b, the output can be made more stable.

A half mirror 1107 is provided on the optical path from the first light source unit 101 to the dichroic mirror 115b. Part of the white light split by the half mirror 1107 enters the photodetector 1109. The photodetector 1109 has a function of detecting the intensity of light, and the detected value is provided to the first light source unit drive control unit 1121 of the control unit 1120 described below. The first light source drive control unit 1121 controls the drive of the white light source of the first light source unit 101 based on the detected value so that the output of white light from the first light source unit 101 becomes constant, for example. To do. In this way, by providing the configuration for monitoring the output of the white light emitted from the first light source unit 101, the output can be made more stable.

The half mirrors 1103 and 1107 are examples of the demultiplexing member, and other demultiplexing members may be used instead of the half mirrors 1103 and 1107. Further, various known photodetectors may be used as the photodetectors 1105 and 1109.

The control unit 1120 controls the operation of the lighting device 1100 in an integrated manner. The control unit 1120 has a first light source unit drive control unit 1121 and a second light source unit drive control unit 1123 as its functions. The control unit 1120 is configured by, for example, a processor such as a CPU (Central Processing Unit) or a DSP (Digital Signal Processor), or a microcomputer including these processors, and these processors perform arithmetic processing according to a predetermined program. By executing, each function of the control unit 1120 is realized.

The first light source unit drive controller 1121 controls the light emission output of the first light source unit 101. Specifically, the first light source unit drive control unit 1121 can control the light emission output by changing the drive current of the white light source (for example, white LED) of the first light source unit 101. As described above, the first light source drive control unit 1121 can monitor the intensity of white light based on the detection value of the photodetector 1109, and the first light source can keep the intensity of white light constant. The drive of the unit 101 can be controlled.

The second light source unit drive control unit 1123 controls the light emission output of the second light source unit 120b. Specifically, the second light source unit drive control unit 1123 can control the light emission output by changing the drive current of the laser light source of the second light source unit 120b. As described above, the second light source unit drive control unit 1123 can monitor the intensity of the laser light based on the detection value of the photodetector 1105, and the second light source can keep the intensity of the laser light constant. The drive of the part 120b can be controlled.

In addition, the second light source unit drive control unit 1123 further has a function of performing control to keep the oscillation wavelength of the laser light source constant by keeping the device temperature of the laser light source of the second light source unit 120b constant. Good. For example, the laser light source has a built-in thermoelectric cooler and a temperature measuring element, and the second light source drive control section 1123 controls driving of the thermoelectric cooler based on the temperature measurement information by the temperature measuring element. Thus, the device temperature of the laser light source can be kept constant.

Here, Table 2 below shows an example of the excitation light wavelength and the fluorescence wavelength of the photosensitive drug used in PDD and PDT.

In this configuration example, the second light source unit 120b is configured to emit laser light corresponding to the excitation light wavelength of the photosensitive drug used. Further, the dichroic mirror 115b attenuates or cuts light corresponding to the excitation light wavelength of the photosensitizer used from the white light emitted from the first light source unit 101, and emits it from the second light source unit 120. Laser light (that is, light corresponding to the excitation light wavelength of the photosensitizing agent used) is transmitted.

In the following, as an example, the configuration and operation of the endoscope device 1 in the case of using laserphyrin as a photosensitizer will be described. In addition, in the configuration example described in the above (2. Second embodiment), the second light source unit 120b multiplexes and emits laser lights in three different wavelength bands, but here, To simplify the description, the second light source unit 120b will be described as emitting only laser light in a wavelength band corresponding to the excitation light wavelength of laserphyrin. This corresponds to the state in which only the laser light source capable of emitting the laser light corresponding to the excitation light wavelength of laserphyrin is driven among the plurality of laser light sources forming the second light source unit 120b.

The characteristics of the dichroic mirror 115b when laserphyrin is used as the photosensitizer will be described with reference to FIGS. 11 and 12. In FIG. 11, the spectrum of the white light emitted from the first light source unit 101, the spectrum of the laser light emitted from the second light source unit 120b, and the transmission characteristic of the dichroic mirror 115b are shown in the same graph. Has been done.

As shown in the figure, the white light emitted from the first light source unit 101 has a wide band emission spectrum including a wavelength band of approximately 400 (nm) to 750 (nm). On the other hand, the laser light emitted from the second light source unit 120b has a narrow-band emission spectrum whose oscillation peak wavelength corresponds to the excitation light wavelength (664 (nm)) of laserphyrin.

Further, the dichroic mirror 115b has a bandpass characteristic of transmitting light in a wavelength band of about several tens (nm) around the wavelength of the excitation light (that is, the peak wavelength of the laser light from the second light source unit 120b). In the illustrated example, the dichroic mirror 115b has a characteristic of transmitting light in a wavelength band of about 20 (nm) centered on the excitation light wavelength (664 (nm)) of laserphyrin.

FIG. 12 shows the spectrum of the light multiplexed by the dichroic mirror 115b. As shown in the figure, in the white light emitted from the first light source unit 101, a component having a bandwidth of about 20 (nm) centered on the excitation light wavelength of lasafylline of 664 (nm) is attenuated to give about 400 (Nm) to 654 (nm) and about 674 (nm) to 750 (nm), and has a wideband spectrum shape divided into two. On the other hand, regarding the laser light emitted from the second light source unit 120b, the spectrum shape after passing through the laser line filter 1101 is maintained as it is. The light obtained by combining the white light emitted from the first light source unit 101 and the laser light emitted from the second light source unit 120b by the dichroic mirror 115b has a spectrum in which these spectra are superposed. That is, in the combined light, the component of the wavelength band corresponding to the excitation light wavelength of laserphyrin is attenuated from the white light emitted from the first light source unit 101, and the attenuated component is the second component. It can be said that it is white light (that is, combined white light) generated by being supplemented by the laser light emitted from the light source unit 120b.

(Endoscope part 1200)
The endoscope section 1200 includes a lens barrel 1210 and an image pickup unit 1220. In this configuration example, the endoscope section 1200 is configured as a rigid endoscope. The lens barrel 1210 has a substantially cylindrical shape, and a light guide 130 (that is, a light guide member) is provided inside the lens barrel 1210 so as to extend to the tip thereof. The lens barrel 1210 is inserted into the body cavity of the patient, and the light guided through the light guide 130 (that is, the output light from the illuminating device 1100) is emitted from the distal end portion, whereby white light is emitted to the observation site 1500. And/or excitation light is applied.

When the observation site 1500 is irradiated with white light and/or excitation light, the reflected light is guided in the opposite direction in the lens barrel 1210 and reaches the imaging unit 1220. In FIG. 10, the propagation of light in the image pickup unit 1220 is schematically shown by a dashed arrow.

The image pickup unit 1220 has an optical filter 1221, a first image pickup element 1223, and a second image pickup element 1225. When the reflected light from the observation region 1500 reaches the imaging unit 1220, it is incident on the optical filter 1221.

The optical filter 1221 is a spectroscopic element such as a dichroic mirror. For example, the optical filter 1221 transmits light having a wavelength of 670 (nm) or more and allows the light to enter the first imaging element 1223, and also transmits light having a wavelength of less than 670 (nm). It is configured to reflect and enter the second image sensor 1225. Therefore, the first imaging element 1223 does not receive the excitation light of the laserphyrin (wavelength 664 (nm)), but receives the fluorescence of the laserphyrin (wavelength 672 (nm)). As described above, the optical filter 1221 is configured such that only the drug fluorescence of the drug excitation light and the drug fluorescence is incident on one of the image pickup devices (the first image pickup device 1223 in the illustrated example).

The first image sensor 1223 and the second image sensor 1225 are image sensors capable of color imaging. The types of the first image sensor 1223 and the second image sensor 1225 are not limited, and examples of the first image sensor 1223 and the second image sensor 1225 include, for example, a CCD (Charge Coupled Device) image sensor and a CMOS (Complementary). Various known image pickup devices such as a metal-oxide-semiconductor image sensor can be used.

The output of the first image sensor 1223 is input to the long wavelength band image generation unit 1301 of the image processing apparatus 1300 described later. The output of the second image sensor 1225 is input to the short wavelength band image generation unit 1303 of the image processing apparatus 1300 described later.

(Image processing apparatus 1300)
The image processing device 1300 generates a captured image (observation image) of the observation site 1500 based on the reflected light from the observation site 1500 detected by the imaging unit 1220. The image processing apparatus 1300 has, as its functions, a long wavelength band image generation unit 1301, a short wavelength band image generation unit 1303, an observation image generation unit 1305, and an input unit 1307. The image processing apparatus 1300 is composed of, for example, a processor such as a CPU or a DSP, or a microcomputer equipped with these processors, and these processors execute arithmetic processing according to a predetermined program, thereby the image processing apparatus 1300. Each function of is realized. For example, the image processing apparatus 1300 may be an information processing apparatus such as a PC (Personal Computer) equipped with a processor and a microcomputer.

The long wavelength band image generation unit 1301 generates an image of the observation site 1500 based on the output signal from the first image sensor 1223. The image generated by the long wavelength band image generation unit 1301 is also referred to as a first image below. Since the first image sensor 1223 receives light having a wavelength of 670 (nm) or more by the optical filter 1221, the long wavelength band image generation unit 1301 causes the long-wavelength band image generation unit 1301 to have a relatively long wavelength of 670 (nm) or more. A first image is generated based on the light in the wavelength band. In this way, the long wavelength band image generation unit 1301 generates the first image based on the light in the wavelength band that is longer than the excitation light wavelength and includes the fluorescence wavelength.

The short wavelength band image generation unit 1303 generates an image of the observation site 1500 based on the output signal from the second image sensor 1225. The image generated by the short wavelength band image generation unit 1303 is also referred to as a second image below. Due to the optical filter 1221, the second image sensor 1225 receives light with a wavelength of less than 670 (nm), so the short wavelength band image generation unit 1303 has a wavelength of less than 670 (nm) and is relatively short. A second image is generated based on the light in the wavelength band. In this way, the short wavelength band image generation unit 1303 generates the second image based on the light in the wavelength band that is shorter than the fluorescence wavelength and includes the excitation light wavelength.

The observation image generation unit 1305 performs observation based on at least one of the first image generated by the long wavelength band image generation unit 1301 and the second image generated by the short wavelength band image generation unit 1303. Generate an image. The image generated by the observation image generation unit 1305 finally becomes the observation image of the observation region 1500 visually recognized by the user. Here, the specific processing of the observation image generation unit 1305 differs depending on the observation mode. Details of the processing of the observation image generation unit 1305 will be described later in (4-2-2. Operation of endoscope apparatus) again. The observation image generation unit 1305 transmits information about the generated image to the display device 1400.

The input unit 1307 is an input interface that receives a user's operation input. The input unit 1307 is configured by an input device operated by a user, such as a mouse, a keyboard, a touch panel, buttons, switches and levers. The user can input various information and various instructions to the endoscope apparatus 1 via the input unit 1307.

For example, the user inputs, via the input unit 1307, to the endoscope device 1 an instruction to select one of the normal observation mode, the special observation mode, and the normal/special observation mode as the observation mode. can do. The information about the selected observation mode is input to the observation image generation unit 1305 and the first light source unit drive control unit 1121 and the second light source unit drive control unit 1123 of the illumination device 1100, and the observation image generation unit 1305 and the first light source. The unit drive control unit 1121 and the second light source unit drive control unit 1123 generate an image or drive the first light source unit 101 and the second light source unit 120 according to the selected observation mode.

Further, for example, the user gives an instruction to the endoscope apparatus 1 via the input unit 1307 about the intensity of the light emitted from the first light source unit 101 and the second light source unit 120 of the illumination device 1100. You can enter. The input information about the intensity is input to the first light source unit drive control unit 1121 and the second light source unit drive control unit 1123 of the lighting device 1100, and the first light source unit drive control unit 1121 and the second light source unit drive control unit. 1123 drives the first light source unit 101 and the second light source unit 120 so that the instructed intensity is realized.

(Display device 1400)
The display device 1400 displays the image generated by the observation image generation unit 1305 of the image processing device 1300. The type of the display device 1400 is not limited, and the display device 1400 may be, for example, a CRT display device, a liquid crystal display device, a plasma display device, an EL display device, or the like. The user visually recognizes the image displayed on the display device 1400 to diagnose or treat the observation site 1500.

The example of the configuration of the endoscope device 1 to which the lighting device 20 is applied has been described above with reference to FIGS. The configuration of the endoscope device 1 shown in FIG. 10 is merely an example, and the specific configuration of the endoscope device 1 may be appropriately changed within the range where the functions described above are realized. For example, the endoscope device 1 may be further provided with various optical elements provided in a general existing endoscope device, in addition to the illustrated configuration.

Further, the respective functions of the control unit 1120 of the lighting device 1100 and the respective functions of the image processing device 1300 do not necessarily have to be mounted in the respective devices as illustrated, and these functions may be executed by any of the devices. Good. For example, some or all of the functions of the control unit 1120 may be installed in the image processing apparatus 1300. Alternatively, conversely, some or all of the functions of the image processing apparatus 1300 may be installed in the lighting apparatus 1100. Further, in the above-described example, an instruction input regarding driving of the lighting device 2100 is performed via the input unit 1307 provided in the image processing device 1300, but the lighting device 2100 also has the same function as the input unit 1307. Alternatively, the user may input various instructions to the lighting device 2100 via the input unit.

(4-2-2. Operation of endoscope apparatus)
The operation of the endoscope apparatus 1 described above according to the observation mode will be described. In the endoscope apparatus 1, as the observation mode, any one of the normal observation mode, the special observation mode, and the normal/special observation mode can be selected.

(Normal observation mode)
In the normal observation mode, broadband light corresponding to visible light in the range of approximately 400 nm to 750 nm is applied to the observation region 1500, and an image of the observation region 1500 is acquired. When the user inputs an instruction to select the normal observation mode as the observation mode via the input unit 1307, the first light source unit drive control unit 1121 and the second light source of the illumination device 1100 are input according to the instruction. The section drive control section 1123 drives both the first light source section 101 and the second light source section 120b.

At this time, as shown in FIG. 12, the output light from the illuminating device 1100 is light (combined light) obtained by combining white light from the first light source unit 101 and laser light from the second light source unit 120b. White light). Here, in the normal observation mode, the output of the laser light from the second light source unit 120b is such that the combined white light has a hue similar to the original white light emitted from the first light source unit 101. It can be adjusted appropriately. That is, the output of the laser light is such that the wavelength band component attenuated or removed by the dichroic mirror 115b is complemented by the laser light from the second light source unit 120b so that the original white light can be reproduced. Can be adjusted.

In the imaging unit 1220, as described above, light having a wavelength of 670 (nm) or more is incident on the first imaging element 1223, and light having a wavelength of less than 670 (nm) is incident on the second imaging element 1225. .. Therefore, the long wavelength band image generation unit 1301 of the image processing device 1300 generates an image based on light in the red band having a wavelength of 670 (nm) or more as the first image. Further, in the short wavelength band image generation unit 1303, an image based on light in the red band, the green band and the blue band having a wavelength of less than 670 (nm) is generated as the second image.

In the normal observation mode, the observation image generation unit 1305 uses the RGB values of the first image generated by the long wavelength band image generation unit 1301 and the RGB values of the second image generated by the short wavelength band image generation unit 1303. A synthetic image is generated by adding and. The composite image generated in this way becomes a normal observation image corresponding to irradiation light in the visible light band (about 400 (nm) to 750 (nm)).

In the above example, the case where both the first light source unit 101 and the second light source unit 120 are driven in the normal observation mode has been described. However, the operation of the endoscope apparatus 1 in the normal observation mode is not limited to this example. Not limited. For example, even if white light in which the light in the wavelength band near 664 (nm), which is the wavelength corresponding to the excitation light of laserphyrin, is removed or reduced by the dichroic mirror 115b does not interfere with the observation of the observation site 1500. May drive only the first light source unit 101.

Further, in the above example, the output of the laser light from the second light source unit 120b is adjusted so that the combined white light has a hue similar to the original white light emitted from the first light source unit 101. However, the operation of the endoscope apparatus 1 in the normal observation mode is not limited to such an example. For example, the output of the white light from the first light source unit 101 and the output of the laser light from the second light source unit 120b are appropriately adjusted so that the combined white light has a predetermined tint preset by the user. (For example, a color shade similar to white light from various standard light sources) may be adjusted within a possible range. In addition, for example, the second light source unit 120b may emit light in the same manner as the second light source unit 120 in the illumination devices 10, 20, 30, 40 in addition to the laser light in the wavelength band corresponding to the excitation light wavelength of laserphyrin. The red laser light, the green laser light, and the blue laser light corresponding to the three primary colors may be emitted. In this case, by appropriately controlling the output of the laser light of each color, the color temperature of the combined white light can be adjusted so as to reproduce the hue of the white light from various arbitrary light sources. Note that such adjustment of the color temperature of the combined white light using the red laser light, the green laser light, and the blue laser light may be performed in the normal/observation mode described later.

(Special observation mode)
In the special observation mode, the narrow band light corresponding to the excitation light wavelength of laserphyrin, which is a photosensitizer, is irradiated on the observation site 1500, and an image based on the fluorescence from the observation site 1500 is acquired. The special observation mode is an observation mode used when performing PDD and PDT.

When the user inputs an instruction to select the special observation mode as the observation mode via the input unit 1307, the second light source unit drive control unit 1123 of the illumination device 1100 causes the second observation by the second light source unit drive control unit 1123 according to the instruction. Only the light source section 120b of is driven.

At this time, the output light from the illuminating device 1100 becomes a light having no white light spectrum in the spectrum shown in FIG. 12, that is, a laser light having the excitation light wavelength of laserphyrin as the central wavelength. In general, in PDT, the observation light 1500 is irradiated with excitation light at a higher intensity than in PDD. Therefore, in the special observation mode, when PDT is performed, the output of the laser light from the second light source unit 120b is set to be stronger than when PDD is performed.

In the imaging unit 1220, as described above, light having a wavelength of 670 (nm) or more is incident on the first imaging element 1223, and light having a wavelength of less than 670 (nm) is incident on the second imaging element 1225. .. Therefore, the long wavelength band image generation unit 1301 of the image processing device 1300 generates an image based on light in the red band having a wavelength of 670 (nm) or more as the first image.

Here, since the fluorescence wavelength of laserphyrin is 672 (nm), the first image generated by the long wavelength band image generation unit 1301 is an image based on the fluorescence of the laserphyrin, that is, observation in the special observation mode. It is an image in which a tumor selectively appears, which is a target. Therefore, in the special observation mode, the observation image generation unit 1305 outputs the first image generated by the long wavelength band image generation unit 1301, that is, the fluorescence observation image to the display device 1400.

(Normal/Special observation mode)
In the normal/special observation mode, irradiation of white light for normal observation and irradiation of excitation light for special observation are performed simultaneously, so that the shape of the operative field can be grasped by the normal observation image and the tumor can be detected by the special observation image. Fluorescence observation can be performed simultaneously. As described above, by performing the observation in the normal/special observation mode, it becomes possible to easily determine at which position in the surgical field the tumor exists.

When the user inputs an instruction to select the normal/special observation mode as the observation mode via the input unit 1307, the first light source of the illumination device 1100 is received according to the instruction as in the normal observation mode. The first light source unit 101 and the second light source unit 120b are both driven by the unit drive control unit 1121 and the second light source unit drive control unit 1123. At this time, as shown in FIG. 12, the output light from the illuminating device 1100 is light (combined light) obtained by combining white light from the first light source unit 101 and laser light from the second light source unit 120b. White light). However, unlike the normal observation mode, in the normal/special observation mode, the output of the laser light from the second light source unit 120b is adjusted to a value according to PDD and PDT. At this time, similarly to the special observation mode, when the PDT is performed, the output of the laser light from the second light source unit 120b is set to be stronger than when the PDD is performed. It

In the imaging unit 1220, as described above, light having a wavelength of 670 (nm) or more is incident on the first imaging element 1223, and light having a wavelength of less than 670 (nm) is incident on the second imaging element 1225. .. Therefore, the long wavelength band image generation unit 1301 of the image processing device 1300 generates an image based on light in the red band having a wavelength of 670 (nm) or more as the first image. Further, in the short wavelength band image generation unit 1303, an image based on light in the red band, the green band and the blue band having a wavelength of less than 670 (nm) is generated as the second image.

Here, since the fluorescence wavelength of laserphyrin is 672 (nm), the first image generated by the long wavelength band image generation unit 1301 is an image based on the fluorescence of the laserphyrin, that is, the tumor selectively. This is the image that appeared. On the other hand, in the second image generated by the short wavelength band image generation unit 1303, the red component is considered to be based on the component of the irradiation light that corresponds to the excitation light wavelength of laserphyrin. It can be said that the red component in such a second image is a component that hinders the fluorescence observation of the tumor.

Therefore, in the normal/special observation mode, the observation image generation unit 1305 has the R value of the first image generated by the long wavelength band image generation unit 1301 and the second R value generated by the short wavelength band image generation unit 1303. A composite image is generated by adding the GB value of the image. The composite image thus generated is an image in which the normal observation image based on the GB value of the second image and the fluorescence observation image based on the R value of the first image are superimposed. In the image, the tumor is displayed in red in the normal observation image based on the BG value.

In the above example, the case where both the first light source unit 101 and the second light source unit 120 are driven in the normal/special observation mode has been described, but the operation of the endoscope apparatus 1 in the normal/special observation mode. Is not limited to such an example. For example, the operation in the normal observation mode and the operation in the special observation mode described above are continuously performed alternately in a time division manner to obtain a normal observation image and a fluorescence observation image, and the observation image generation unit 1305 By combining these, an image in which the normal observation image and the fluorescence observation image are superimposed may be acquired.

Further, in the above example, the finally obtained image may be one in which the tumor is displayed in red in the normal observation image based on the BG value. However, the tumor displayed in red is not always easy for the user to visually recognize. Therefore, based on the user's request, the observation image generation unit 1305 may further perform image processing for appropriately changing the display color of the tumor. Thereby, the visibility of the tumor by the user can be further improved.

The configuration and operation of the endoscope device 1 incorporating the illumination device 1100 having substantially the same configuration as the illumination device 20 according to the second embodiment have been described above. By using the lighting device 1100 as the light source of the endoscope device 1, the following effects can be obtained as with the lighting device 20.

That is, the illumination device 1100 is provided with the diffusion member 111 on the optical path of the laser light from the second light source unit 120b, and the emission angle of the laser light is expanded by the diffusion member 111. Generally, the white LED used in the first light source unit 101 has a larger beam diameter and emission angle than the laser light source (for example, a semiconductor laser) used in the second light source unit 120b. Therefore, by expanding the emission angle of the laser light from the second light source unit 120b using the diffusion member 111, the white light from the first light source unit 101 and the second light source at the incident end face of the light guide 130 are obtained. It is possible to ensure substantially the same beam diameter and incident angle of the laser light from the portion 120b, that is, to make the beam diameter and emission angle at the output end of the light guide 130 substantially the same. Therefore, the brightness distribution of the irradiation light in the observation region 1500 can be made substantially the same, and the color unevenness of the irradiation light can be reduced.

Further, in the illuminating device 1100, the condenser optical system 117 is configured to image the light from the secondary light source so as to fill the area of the incident end of the light guide 130 as much as possible. As a result, speckle noise of the entire lighting device 10 can be reduced. Therefore, it is possible to obtain a higher quality observation image with reduced speckle noise.

Furthermore, the endoscope device 1 can obtain the following effects.

In the illuminating device 1100, white light from the first light source unit 101 and laser light from the second light source unit 120b are combined on the same optical axis. Therefore, the white light from the first light source unit 101 is used as the irradiation light and the laser light from the second light source unit 120b is used as the irradiation light due to the undulations of the observation region 1500. The resulting shadow is observed with the same shape. Therefore, there is no possibility that a portion where no shadow is present during normal observation will be present during fluorescence observation, and that excitation light cannot be applied to that portion. Therefore, the user can more smoothly perform a series of operations of irradiating the target portion in the normal observation mode with the excitation light in the special observation mode, thereby improving the convenience for the user.

Further, in the illumination device 1100, the first light source unit 101 is composed of, for example, a white LED, and the second light source unit 120b is composed of, for example, a semiconductor laser. As described above, when the first light source unit 101 and the second light source unit 120b are configured by the semiconductor light emitting element, the output of the emitted light from each light source unit is controlled by appropriately controlling the drive current. It becomes possible to control independently at any timing. Therefore, the output light from the lighting device 1100 can be adjusted with a higher degree of freedom.

Note that, in the application example described above, for simplicity, the case where only the laser light in the wavelength band corresponding to the excitation light wavelength of the photosensitizing agent is emitted from the second light source unit 120b has been described. In the same manner as in the illumination devices 10, 20, 30, and 40, the second light source unit 120b may emit laser light in a plurality of wavelength bands different from each other. In the case where the second light source section 120b is configured in this way, by controlling the output of each laser light independently as described above, it can be used as irradiation light in the normal observation mode and the normal/special observation mode. It is possible to more easily adjust the color temperature of the white wave light.

Further, in the illumination device 1100, the photodetectors 1105 and 1109 for detecting the intensities of the white light from the first light source unit 101 and the laser light from the second light source unit 120b before being combined. Is provided. Then, the driving of the first light source unit 101 and the second light source unit 120b is controlled according to the intensities of the white light and the laser light monitored by the photodetectors 1105 and 1109. Therefore, the intensity of the light emitted from the first light source unit 101 and the second light source unit 120b can be controlled with higher accuracy, and the quality of the output light from the lighting device 1100 can be further improved.

Further, in the illumination device 1100, the dichroic mirror 115b attenuates or removes the light in the predetermined wavelength band from the white light from the first light source unit 101, and the white light is attenuated or removed. The laser light from the second light source unit 120b is combined so as to supplement the component of the wavelength band. Further, at that time, the output of the laser light from the second light source unit 120b can be appropriately adjusted so that the combined light has a hue similar to the original white light. Therefore, when performing the observation using the combined white light in the normal observation mode and the normal/special observation mode, it is possible to minimize the change in the hue of the observation region 1500 that is felt by the user.

Further, in the endoscopic device 1, in the special observation mode and the normal/special observation mode, the optical filter 1221 prevents the light in the wavelength band corresponding to the excitation light from entering the first image sensor 1223 and corresponds to the fluorescence. The image pickup unit 1220 is configured such that the light in the wavelength band to be incident is incident. As described above, according to this application example, with the relatively simple configuration of the optical filter 1221, the weak fluorescent component emitted from the observation region 1500 can be detected with high accuracy, and a higher-definition fluorescent observation image can be obtained. Can be obtained.

Further, in the endoscope apparatus 1, the processing by the observation image generation unit 1305 is appropriately switched according to the observation mode, so that the operation field is confirmed by the normal observation image in the normal observation mode, and the fluorescence observation in the special observation mode is performed. It is possible to appropriately perform tumor diagnosis based on an image and position confirmation of a tumor in a surgical field with an image obtained by superimposing a normal observation image and a fluorescence observation image in the normal/special observation mode, according to a user's request. Particularly, in the normal/special observation mode, it is possible to obtain an image in which the normal observation image and the fluorescence observation image are superimposed while simultaneously irradiating the white light and the excitation light in a time-division manner. Therefore, it becomes possible to observe the tumor in the surgical field in real time. Further, in this application example, image acquisition in the normal/special observation mode is performed by the optical filter 1221, the plurality of image pickup devices (the first image pickup device 1223 and the second image pickup device 1225), and the image processing apparatus 1300. Each function (long wavelength band image generation unit 1301, short wavelength band image generation unit 1303, and observation image generation unit 1305) can be executed with a relatively simple configuration. Therefore, it is possible to obtain a higher quality observation image in the normal/special observation mode without increasing the size of the apparatus and increasing the cost.

(4-2-3. Another configuration example of the endoscope apparatus)
As another modification of the endoscope apparatus 1 described above, another configuration example of the endoscope apparatus 1 will be described with reference to FIG. 13. 13: is a figure which shows the other structural example of the endoscope apparatus 1 shown in FIG. The endoscope apparatus according to the present modification corresponds to the endoscope apparatus 1 shown in FIG. 10 in which the configuration of the endoscope section 1200 is changed. Therefore, FIG. 13 illustrates only the endoscope section 1200c in the configuration of the endoscope apparatus according to the present modification.

Referring to FIG. 13, the endoscope section 1200c of the endoscope apparatus according to the present modification includes a lens barrel 1210 and an imaging unit 1220c. Here, the configuration and function of the lens barrel 1210 are the same as the configuration and function of the lens barrel 1210 shown in FIG. On the other hand, the image pickup unit 1220c has an optical filter 1221, a first image pickup element 1223, a second image pickup element 1225, and a second optical filter 1227. As described above, the image pickup unit 1220c according to the present modification corresponds to the image pickup unit 1220 of the endoscope apparatus 1 shown in FIG. 10 in which the second optical filter 1227 is further provided.

As shown in the figure, the second optical filter 1227 is provided in front of the second image sensor 1225. The second optical filter 1227 blocks only light corresponding to the wavelength band of the laser light from the second light source unit 120b (for example, light in the wavelength band corresponding to the excitation light wavelength (664 (nm)) of laserphyrin). It is a notch filter. By providing the second optical filter 1227, the amount of light received by the second image sensor 1225 in the wavelength band corresponding to the excitation light wavelength of laserphyrin is suppressed.

In this modified example, the processing in the observation image generation unit 1305 in the normal observation mode and the special observation mode is the same as the processing in the endoscope device 1 described above. However, the processing in the observation image generation unit 1305 in the normal/special observation mode is slightly different from the processing in the endoscope device 1 described above.

Specifically, in the normal/special observation mode, both the first light source unit 101 and the second light source unit 120b are driven, and the white light from the first light source unit 101 and the second light source unit 120b are driven. The light combined with the laser light is applied to the observation region 1500. At this time, the output of the laser light from the second light source unit 120b is adjusted to a value according to PDD and PDT.

In the imaging unit 1220c, light having a wavelength of 670 (nm) or more is incident on the first imaging element 1223, and light having a wavelength of less than 670 (nm) is incident on the second imaging element 1225. However, from the light incident on the second image sensor 1225, the component of the wavelength band corresponding to the excitation light wavelength of laserphyrin is cut off.

In the long wavelength band image generation unit 1301 of the image processing device 1300, an image showing a tumor based on red band light having a wavelength of 670 (nm) or more is generated as the first image. Further, in the short wavelength band image generation unit 1303, an image based on light in the red band, the green band and the blue band having a wavelength of less than 670 (nm) is generated as the second image. However, from the second image generated by the short wavelength band image generation unit 1303, the component of the wavelength band corresponding to the excitation light wavelength of laserphyrin is cut off.

In this modification, the observation image generation unit 1305 adds the RGB values of the image generated by the long wavelength band image generation unit 1301 and the RGB values of the image generated by the short wavelength band image generation unit 1303. To generate a composite image. Since the component of the wavelength band corresponding to the excitation light wavelength of laserphyrin is cut from the second image generated by the short wavelength band image generation unit 1303, by simply adding the RGB values of both images, An image in which the normal observation image and the fluorescence observation image are superposed can be obtained.

Here, particularly when PDT is performed, the intensity of the laser light from the second light source unit 120b is much higher than the intensity of the white light from the first light source unit 101. Therefore, when an image is generated based on the light corresponding to the wavelength band of the laser light from the second light source unit 120b, the amount of light received in the wavelength band is saturated and a normal image cannot be generated. There is a nature. Therefore, in the above-described endoscope apparatus 1, in the normal/special observation mode, by adding the R value of the first image and the GB value of the second image, the second light source is, so to speak, at the stage of image processing. The component corresponding to the wavelength band of the laser light from the section 120b is cut to generate the composite image. On the other hand, in the present modification, the second optical filter 1227 is provided in front of the second image sensor 1225, and the light corresponding to the wavelength band of the laser light from the second light source unit 120b to the second image sensor 1225 is provided. It is possible to obtain an image in which the component of the wavelength band of the laser light is cut by simply adding the RGB value of the first image and the RGB value of the second image by blocking the incidence of Of.

(4-3. Microscope device)
(4-3-1. Configuration of microscope device)
With reference to FIG. 14 and FIG. 15, a configuration of the microscope device when the illumination devices 10, 20, 30, 40 are applied to the microscope device will be described. FIG. 14: is a figure which shows one structural example of the microscope apparatus to which the illuminating device 10, 20, 30, 40 which concerns on 1st Embodiment, 2nd Embodiment, and each modification is applied. FIG. 15 is an explanatory diagram for explaining the irradiation range of irradiation light in the observation region 1500.

Note that, in the following description, as an example, a case will be described in which a configuration corresponding to the illumination device 10 according to the first embodiment is installed in a microscope device. As will be described later, when the illuminating devices 10, 20, 30, and 40 are applied to the microscope device, in order to accurately control the irradiation intensity of the excitation light with respect to the observation site 1500 when PDT is performed, It is preferable to use an illuminating device such as the device 10 in which the optical fiber 107 is mounted. However, this application example is not limited to such an example, and configurations corresponding to the other illumination devices 20, 30, and 40 may be installed in the microscope device.

Referring to FIG. 14, the microscope device 2 includes an illumination device 2100, an imaging unit 2200, an image processing device 1300, and a display device 1400. In addition, in FIG. 14, the observation site 1500 to which the output light from the illumination device 2100 is irradiated is also schematically illustrated.

(Lighting device 2100)
The illumination device 2100 generates white light for normal observation (combined white light) and excitation light for fluorescence observation. White light and/or excitation light generated by the illuminating device 2100 is projected to the outside via a projection lens 1111 described below, and is irradiated to the observation site 1500.

Here, the lighting device 2100 corresponds to the lighting device 10 according to the first embodiment described above. However, when mounted on the microscope apparatus 2, some members are omitted and added.

Specifically, the illumination device 2100 includes a first light source unit 101 that emits white light, a first collimating optical system 103, and a second light source that emits light in a predetermined wavelength band. Light source unit 120b, coupling optical system 105, optical fiber 107, third collimating optical system 109, dichroic mirror 115b, condenser optical system 117, laser line filter 1101, half mirror 1103, and light detection. It has a device 1105, a half mirror 1107, a photodetector 1109, and a controller 1120.

As described above, in the lighting device 2100, the laser line filter 1101, the half mirror 1103, the photodetector 1105, the half mirror 1107, and the photodetector 1109 are added to the lighting device 10 according to the first embodiment. , The second collimating optical system 113 and the diffusing member 111 are omitted. Further, in the lighting device 2100, the optical characteristics of the second light source unit 120 and the dichroic mirror 115 are also changed from those of the lighting device 10 according to the first embodiment. The configurations and functions of the other members are the same as the configurations and functions of these respective members shown in FIG. 1, and thus detailed description of each of these members will be omitted. The control unit 1120 corresponds to a control unit (not shown in FIG. 1) that controls driving of the first light source unit 101 and the second light source unit 120b.

Here, the configurations and functions of the second light source unit 120b, the dichroic mirror 115b, the laser line filter 1101, the half mirror 1103, the photodetector 1105, the half mirror 1107, the photodetector 1109, and the control unit 1120 are shown in FIG. Since the configurations and functions of these members in the endoscope apparatus 1 are the same, detailed description thereof will be omitted.

As illustrated, in the illumination device 2100, the laser light emitted from the second light source unit 120b passes through the coupling optical system 105, the optical fiber 107, the third collimating optical system 109, the laser line filter 1101 and the half mirror 1103. The light passes through this order and enters the dichroic mirror 115b as substantially parallel light. On the other hand, the white light emitted from the first light source unit 101 passes through the first collimating optical system 103 and enters the dichroic mirror 115b as substantially parallel light.

A projection lens 1111 is provided in a partial region of the partition wall of the housing of the lighting device 2100, and the light passing through the dichroic mirror 115b is applied to the observation site 1500 via the projection lens 1111.

Here, in the following, as an example, the configuration and operation of the microscope device 2 in the case where laserphylline is used as the photosensitizer, as in the endoscope device 1, will be described. In addition, in the configuration example described in the above (1. First embodiment), the second light source unit 120 multiplexes and emits laser lights in three different wavelength bands, but here, To simplify the description, the second light source unit 120b will be described as emitting only laser light in a wavelength band corresponding to the excitation light wavelength of laserphyrin. This corresponds to the state in which only the laser light source capable of emitting the laser light corresponding to the excitation light wavelength of laserphyrin is driven among the plurality of laser light sources forming the second light source unit 120b.

Note that the characteristics of the dichroic mirror 115b in the case of using laserphyrin are similar to the characteristics described above with reference to FIGS. 11 and 12. That is, the white light emitted from the first light source unit 101 and the laser light emitted from the second light source unit 120b are combined by the dichroic mirror 115b, and the white light emitted from the first light source unit 101 is obtained. A component in a wavelength band corresponding to the excitation light wavelength of laserphyrin is attenuated or removed from the light, and the attenuated or removed component is generated by being complemented by the laser light emitted from the second light source unit 120b. It becomes white light (that is, combined white light).

FIG. 15 shows an example of the irradiation range of the observation site 1500 when the combined white light is applied to the observation site 1500. As shown in FIG. 15, when both the white light emitted from the first light source unit 101 and the laser light emitted from the second light source unit 120b irradiate the observation region 1500, particularly in the normal/special observation mode. In such a case, the second irradiation range 1503 by the laser light from the second light source unit 120b is irradiated so that it is included in the first irradiation range 1501 by the white light from the first light source unit 101. It is preferable that the ranges 1501 and 1503 are adjusted. When the irradiation ranges 1501 and 1503 have the relationship shown in the drawing, for example, when PDD or PDT is performed, normal observation of the observation region 1500 is performed by the white light from the first light source unit 101, and the normal observation is performed. It is possible to intensively irradiate the targeted portion with the laser light (that is, the excitation light) from the second light source unit 120b.

The adjustment of the first irradiation range 1501 and the second irradiation range 1503 can be controlled by adjusting the core diameter of the optical fiber 107, the focal length of the third collimating optical system 109, and the focal length of the projection lens 1111. .. At this time, it is desirable that the optical characteristics of each member be adjusted so that the image on the emission end face of the optical fiber 107 forms an image on the observation site 1500. In this case, since the emission end of the optical fiber 107 and the observation region 1500 can be conjugated, adjusting the intensity and size of the laser light on the emission end face of the optical fiber 107 causes the irradiation laser light of the observation region 1500 to be changed. This is because the strength and size can be adjusted.

Here, when performing PDT, for example, the intensity per unit time and unit area of the excitation light with which the affected area (tumor) is irradiated is determined according to the type of the tumor or the type of the photosensitizing agent. Is common. Therefore, in the microscope apparatus 2, it is possible to perform PDT more effectively by appropriately adjusting the intensity and size of the laser light with which the observation region 1500 is irradiated using the optical fiber 107 as described above. Become.

In the microscope apparatus 2, the optical fiber 107 is provided, and the intensity and size of the laser light at the emission end of the optical fiber 107, which can be conjugated with the observation site 1500, are appropriately adjusted, so that the irradiation laser beam on the observation site 1500 can be changed. It is possible to adjust the strength and size. Therefore, in order to precisely control the irradiation of the excitation light to the observation region 1500 when performing PDT, it is preferable that the microscope apparatus 2 be provided with the optical fiber 107 as shown in the figure.

(Imaging unit 2200)
The image pickup unit 2200 includes an optical filter 1221, a first image pickup element 1223, a second image pickup element 1225, and an image lens 2227. The image lens 2227 is provided in a partial region of the partition wall of the housing of the imaging unit 2200, and guides the reflected light from the observation site 1500 into the housing. The light guided into the housing of the imaging unit 2200 via the image lens 2227 enters the optical filter 1221 provided in the housing. Note that, in FIG. 14, propagation of light in the imaging unit 2200 is schematically illustrated by a dashed arrow.

The configurations and functions of the optical filter 1221, the first image sensor 1223, and the second image sensor 1225 are the same as the configurations and functions of these members in the endoscope apparatus 1 shown in FIG. 10, and therefore detailed description thereof. Is omitted. That is, the reflected light from the observation region 1500 is separated by the optical filter 1221 into, for example, light having a wavelength of 670 (nm) or more and light having a wavelength of less than 670 (nm), and light having a wavelength of 670 (nm) or more. Is incident on the first image sensor 1223, and light having a wavelength of less than 670 (nm) is incident on the second image sensor 1225.

(Image processing apparatus 1300)
The image processing apparatus 1300 generates a captured image (observation image) of the observation site 1500 based on the reflected light from the observation site 1500 detected by the imaging unit 2200. The configuration and function of the image processing apparatus 1300 are the same as the configuration and function of the image processing apparatus 1300 in the endoscope apparatus 1 shown in FIG. 10, and therefore detailed description thereof will be omitted.

(Display device 1400)
The display device 1400 displays the image generated by the observation image generation unit 1305 of the image processing device 1300. Since the configuration and function of the display device 1400 are the same as the configuration and function of the display device 1400 in the endoscope device 1 shown in FIG. 10, detailed description thereof will be omitted.

(4-3-2. Operation of microscope device)
The operation of the microscope apparatus 2 described above according to the observation mode will be described. In the microscope apparatus 2, as the observation mode, any one of the normal observation mode, the special observation mode, and the normal/special observation mode can be selected. The operation of the microscope apparatus 2 according to each observation mode is the same as the operation of the endoscope apparatus 1 shown in FIG. 10 according to each observation mode, and thus detailed description of overlapping matters will be omitted.

(Normal observation mode)
In the normal observation mode, broadband light corresponding to visible light in the range of approximately 400 nm to 750 nm is applied to the observation region 1500, and an image of the observation region 1500 is acquired.

When the user selects the normal observation mode as the observation mode, both the first light source unit 101 and the second light source unit 120b of the illumination device 2100 are driven. At this time, as shown in FIG. 12, the output light from the illuminating device 1100 is a light obtained by combining white light from the first light source unit 101 and laser light from the second light source unit 120 (combined light). White light). Here, in the normal observation mode, the output of the laser light from the second light source unit 120b is such that the combined white light has a hue similar to the original white light emitted from the first light source unit 101. It can be adjusted appropriately.

In the imaging unit 2200, light having a wavelength of 670 (nm) or more enters the first imaging element 1223, and light having a wavelength of less than 670 (nm) enters the second imaging element 1225, as described above. Therefore, the long wavelength band image generation unit 1301 of the image processing device 1300 generates an image based on light in the red band having a wavelength of 670 (nm) or more as the first image. Further, in the short wavelength band image generation unit 1303, an image based on light in the red band, the green band and the blue band having a wavelength of less than 670 (nm) is generated as the second image.

In the normal observation mode, the observation image generation unit 1305 adds the RGB values of the image generated by the long wavelength band image generation unit 1301 and the RGB values of the image generated by the short wavelength band image generation unit 1303. To generate a composite image. The composite image generated in this way becomes a normal observation image corresponding to irradiation light in the visible light band (about 400 (nm) to 750 (nm)).

(Special observation mode)
In the special observation mode, the observation site 1500 is irradiated with light in a narrow band corresponding to the excitation light wavelength of laserphyrin, which is a photosensitizer, and an image based on fluorescence from the observation site 1500 is acquired. The special observation mode is an observation mode used when performing PDD and PDT.

When the user selects the special observation mode as the observation mode, only the second light source unit 120 of the illumination device 1100 is driven. At this time, the output light from the illuminating device 1100 is a light having no white light spectrum in the spectrum shown in FIG. 12, that is, a laser light having the excitation light wavelength of laserphyrin as the central wavelength. In the special observation mode, when PDT is performed, the output of the laser light from the second light source unit 120 is set to be stronger than when PDD is performed.

In the imaging unit 2200, light having a wavelength of 670 (nm) or more enters the first imaging element 1223, and light having a wavelength of less than 670 (nm) enters the second imaging element 1225, as described above. Therefore, the long wavelength band image generation unit 1301 of the image processing device 1300 generates an image based on light in the red band having a wavelength of 670 (nm) or more as the first image.

Here, since the fluorescence wavelength of laserphyrin is 672 (nm), the first image generated by the long wavelength band image generation unit 1301 is an image based on the fluorescence of the laserphyrin, that is, observation in the special observation mode. It is an image in which a tumor selectively appears, which is a target. Therefore, in the special observation mode, the observation image generation unit 1305 outputs the image generated by the long wavelength band image generation unit 1301, that is, the fluorescence observation image to the display device 1400.

(Normal/Special observation mode)
In the normal/special observation mode, irradiation of white light for normal observation and irradiation of excitation light for special observation are performed simultaneously, so that the shape of the operative field can be grasped by the normal observation image and the tumor can be detected by the special observation image. Fluorescence observation can be performed simultaneously.

When the user selects the normal/special observation mode as the observation mode, both the first light source unit 101 and the second light source unit 120b of the illumination device 1100 are driven as in the normal observation mode. At this time, as shown in FIG. 12, the output light from the illuminating device 1100 is light (combined light) obtained by combining white light from the first light source unit 101 and laser light from the second light source unit 120b. White light). However, unlike the normal observation mode, in the normal/special observation mode, the output of the laser light from the second light source unit 120b is adjusted to a value according to PDD and PDT. Further, similarly to the special observation mode, when the PDT is performed, the output of the laser light from the second light source unit 120b is set to be stronger than when the PDD is performed.

In the imaging unit 2200, light having a wavelength of 670 (nm) or more enters the first imaging element 1223, and light having a wavelength of less than 670 (nm) enters the second imaging element 1225, as described above. Therefore, the long wavelength band image generation unit 1301 of the image processing device 1300 generates an image based on light in the red band having a wavelength of 670 (nm) or more as the first image. Further, in the short wavelength band image generation unit 1303, an image based on light in the red band, the green band and the blue band having a wavelength of less than 670 (nm) is generated as the second image.

Here, since the fluorescence wavelength of laserphyrin is 672 (nm), the first image generated by the long wavelength band image generation unit 1301 is an image based on the fluorescence of the laserphyrin, that is, the tumor selectively. This is the image that appeared. On the other hand, in the second image generated by the short wavelength band image generation unit 1303, the red component is considered to be based on the component of the irradiation light that corresponds to the excitation light wavelength of laserphyrin. It can be said that the red component in such a second image is a component that hinders the fluorescence observation of the tumor.

Therefore, in the normal/special observation mode, the observation image generation unit 1305 has the R value of the first image generated by the long wavelength band image generation unit 1301 and the second R value generated by the short wavelength band image generation unit 1303. A composite image is generated by adding the GB value of the image. The composite image generated in this way is an image in which the normal observation image based on the GB value of the second image and the fluorescence observation image based on the R value of the first image are superimposed. In the image, the tumor is displayed in red in the normal observation image based on the BG value.

The configuration and operation of the microscope device 2 incorporating the illumination device 2100 having substantially the same configuration as the illumination device 10 according to the first embodiment have been described above. According to the microscope device 2, the following effects can be obtained as in the endoscope device 1 described above.

In the illuminating device 2100, white light from the first light source unit 101 and laser light from the second light source unit 120b are combined on the same optical axis. Therefore, the white light from the first light source unit 101 is used as the irradiation light and the laser light from the second light source unit 120b is used as the irradiation light due to the undulations of the observation region 1500. The resulting shadow is observed with the same shape. Therefore, there is no possibility that a portion where no shadow is present during normal observation will be present during fluorescence observation, and that excitation light cannot be applied to that portion. Therefore, the user can more smoothly perform a series of operations of irradiating the target portion in the normal observation mode with the excitation light in the special observation mode, thereby improving the convenience for the user.

Further, in the illumination device 2100, the first light source unit 101 is composed of, for example, a white LED, and the second light source unit 120b is composed of, for example, a semiconductor laser. As described above, when the first light source unit 101 and the second light source unit 120b are configured by the semiconductor light emitting element, the output of the emitted light from each light source unit is controlled by appropriately controlling the drive current. It becomes possible to control independently at any timing. Therefore, the output light from the lighting device 1100 can be adjusted with a higher degree of freedom.

Note that, in the application example described above, for simplicity, the case where only the laser light in the wavelength band corresponding to the excitation light wavelength of the photosensitizing agent is emitted from the second light source unit 120b has been described. In the same manner as in the lighting devices 10, 20, 30, and 40, a plurality of laser lights having different wavelength bands from each other (for example, red laser light and green laser light corresponding to the three primary colors of light) are emitted from the second light source unit 120b. And blue laser light) may be emitted. When the second light source unit 120b is configured in this way, the combined white light used as irradiation light in the normal observation mode and the normal/special observation mode is controlled by controlling the output of the laser light of each color independently. It becomes possible to more easily adjust the color temperature of the.

Further, in the illumination device 2100, photodetectors 1105 and 1109 for detecting the intensities of the white light from the first light source unit 101 and the laser light from the second light source unit 120b before being combined. Is provided. Then, the driving of the first light source unit 101 and the second light source unit 120b is controlled according to the intensities of the white light and the laser light monitored by the photodetectors 1105 and 1109. Therefore, the intensity of the light emitted from the first light source unit 101 and the second light source unit 120b can be controlled with higher accuracy, and the quality of the output light from the lighting device 2100 can be further improved.

Further, in the illumination device 2100, the dichroic mirror 115b attenuates or removes the light in the predetermined wavelength band from the white light from the first light source unit 101, and the white light is attenuated or removed. The laser light from the second light source unit 120b is combined so as to supplement the component of the wavelength band. Further, at that time, the output of the laser light from the second light source unit 120b can be appropriately adjusted so that the combined light has a hue similar to the original white light. Therefore, when performing the observation using the combined white light in the normal observation mode and the normal/special observation mode, it is possible to minimize the change in the hue of the observation region 1500 that is felt by the user.

Further, in the microscope apparatus 2, in the special observation mode and the normal/special observation mode, the optical filter 1221 prevents the light in the wavelength band corresponding to the excitation light from entering the first image sensor 1223, and the wavelength corresponding to the fluorescence. The imaging unit 2200 is configured so that the light in the band is incident. As described above, according to this application example, with the relatively simple configuration of the optical filter 1221, the weak fluorescent component emitted from the observation region 1500 can be detected with high accuracy, and a higher-definition fluorescent observation image can be obtained. Can be obtained.

Further, in the microscope apparatus 2, the processing by the observation image generation unit 1305 is appropriately switched according to the observation mode, so that the operation field can be confirmed by the normal observation image in the normal observation mode and the fluorescence observation image by the special observation mode. Tumor diagnosis and confirmation of the position of the tumor in the surgical field by the image in which the normal observation image and the fluorescence observation image are superimposed in the normal/special observation mode can be appropriately performed according to the user's request. Particularly, in the normal/special observation mode, it is possible to obtain an image in which the normal observation image and the fluorescence observation image are superimposed while simultaneously irradiating the white light and the excitation light in a time-division manner. Therefore, it becomes possible to observe the tumor in the surgical field in real time. Further, in this application example, image acquisition in such a normal/special observation mode is performed by the optical filter 1221, the plurality of image pickup devices (first image pickup device 1223 and second image pickup device 1225), and the image processing apparatus 1300. Each function (long wavelength band image generation unit 1301, short wavelength band image generation unit 1303, and observation image generation unit 1305) can be executed with a relatively simple configuration. Therefore, it is possible to obtain a higher quality observation image in the normal/special observation mode without increasing the size of the apparatus and increasing the cost.

(5. Supplement)
Although the preferred embodiments of the present disclosure have been described above in detail with reference to the accompanying drawings, the technical scope of the present disclosure is not limited to such examples. It is obvious that a person having ordinary knowledge in the technical field of the present disclosure can come up with various changes or modifications within the scope of the technical idea described in the claims. It is understood that the above also naturally belongs to the technical scope of the present disclosure.

Further, the effects described in the present specification are merely illustrative or exemplary, and are not limiting. That is, the technique according to the present disclosure may have other effects that are apparent to those skilled in the art from the description of the present specification, in addition to or instead of the above effects.

The following configurations also belong to the technical scope of the present disclosure.
(1) A first light source unit that emits broadband light, a second light source unit that emits narrowband light having a wavelength band narrower than the broadband light, and the narrowband light that is emitted from the second light source unit A radiation angle changing member for generating a secondary light source by changing the radiation angle of the light source, the wideband light emitted from the first light source unit, and the narrowband light emitted from the secondary light source. The radiation angle changing member is configured so that the incident angles of the wideband light and the narrowband light are close to each other at the incident end face of the light guide on which the light multiplexed by the multiplexing member is incident. An illumination device for changing the emission angle of the narrow band light.
(2) The emission angle changing member further changes the emission angle of the narrowband light so that the beam diameters of the wideband light and the narrowband light are close to each other at the incident end face of the light guide. ).
(3) The illumination device according to (1) or (2), wherein the combining member is a dichroic mirror, a polarization beam splitter, or a beam splitter.
(4) The second light source unit includes a plurality of light sources that emit the narrow band light, and the emission angle changing member includes the plurality of light sources so that the divergence angles of the plurality of narrow band lights are aligned. The illumination device according to any one of (1) to (3), wherein the emission angle of the narrow band light is changed.
(5) The illumination according to any one of (1) to (4), wherein the first light source unit is at least one of a white LED, a laser-excited phosphor, a xenon lamp, and a halogen lamp. apparatus.
(6) A first collimating optical system that makes the broad band light emitted from the first light source unit substantially parallel light, and a first collimating optical system that makes the narrow band light emitted from the radiation angle changing member substantially parallel light. And a second collimating optical system. The illuminating device according to any one of (1) to (5), wherein the illuminating device combines the narrowband light that has been generated.
(7) Coupling optical system that couples the narrowband light emitted from the second light source unit to an optical fiber, and third collimating optics that makes the narrowband light emitted from the optical fiber into substantially parallel light. The system further comprises: (6), wherein the radiation angle changing member generates a secondary light source by changing a radiation angle of the narrow band light emitted from the third collimating optical system. Lighting equipment.
(8) A condenser optical system for forming an image of the light combined by the combining member on an incident end of the light guide, wherein the condenser optical system forms an image on the incident end of the light guide. The light from the secondary light source is focused on the incident end of the light guide so that the size of the image of the secondary light source is substantially the same as the diameter of the incident end of the light guide. The illumination device according to any one of 7).
(9) The second light source unit includes a plurality of narrow band light sources, and the plurality of narrow band light sources emit a red narrow band light and a green narrow band light source that emits a green narrow band light. The illumination device according to any one of (1) to (8), which further includes at least a blue narrowband light source that emits blue narrowband light.
(10) The second light source unit has a plurality of narrow band light sources, and the driving of the plurality of narrow band light sources is independently controlled, so that the color temperature of the light combined by the combining member is increased. The illumination device according to any one of (1) to (9), wherein is adjusted.
(11) At least one of the narrow-band light sources constituting the second light source section emits narrow-band light in a wavelength band corresponding to excitation light used for fluorescence observation of an observation site, (1) The lighting device according to any one of to (10).
(12) A third light source unit that emits light in a wavelength band different from the narrow band light emitted from the second light source unit, and the broadband light emitted from the first light source unit. Light obtained by combining the light emitted from the third light source unit is incident on the combining member, and the combining member causes the broadband light emitted from the first light source unit and the third light. Any of the above (1) to (11), wherein the light combined with the light emitted from the light source section is combined with the narrow band light emitted from the second light source section. The lighting device according to item 1.
(13) The illumination device according to (12), wherein the first light source unit and the third light source unit are configured by LEDs.
(14) The broadband light is emitted from the first light source unit, the narrow band light having a wavelength band narrower than the broadband light is emitted from the second light source unit, and the second angle is changed by the radiation angle changing member. A secondary light source is generated by changing an emission angle of the narrowband light emitted from the light source unit, and the wideband light emitted from the first light source unit and the secondary light source are combined by a multiplexing member. Combining the narrow band light emitted from the radiation angle changing member, the radiation angle changing member, the broad band light and the wide band light at the incident end face of the light guide on which the light combined by the combining member is incident. A lighting method, wherein the emission angle of the narrow band light is changed so that the incident angle with the narrow band light approaches.
(15) An illumination device that outputs at least one of broadband light and excitation light that is emitted to the operative field of a patient, wherein the illumination device includes a first light source unit that emits broadband light and the broadband light. A second light source unit that emits narrow-band light in a narrow wavelength band; and a radiation angle changing member that changes the radiation angle of the narrow-band light emitted from the second light source unit to generate a secondary light source. A combining member configured to combine the wideband light emitted from the first light source unit and the narrowband light emitted from the secondary light source, wherein the radiation angle changing member includes the combining unit. An observation device that changes the emission angle of the narrowband light so that the incident angles of the wideband light and the narrowband light come close to each other at the incident end surface of the light guide on which the light multiplexed by the member enters.
(16) The observation device according to (15), wherein the intensity of the narrowband light is adjusted according to the purpose of observation of the surgical field.
(17) The observation device is inserted into a body cavity of a patient, the output light from the illumination device is guided inside, and a lens barrel that irradiates the output light to a surgical field in the body cavity, The observation apparatus according to (15) above, which is further an endoscopic apparatus.
(18) The observation device according to (15), which is a microscope device further including a projection lens that irradiates the surgical field with the output light from the illumination device.
(19) A long wavelength band image generation unit that generates a first image based on light having a wavelength band longer than that of the excitation light and including a wavelength band of fluorescence due to the excitation light, and a wavelength band shorter than the fluorescence. And a short wavelength band image generation unit that generates a second image based on light including the wavelength band of the excitation light, according to any one of (15) to (18) above. Observation device.
(20) In the normal observation mode in which a normal observation image of the surgical field is obtained by the broadband light, the first light source unit and the second light source unit are both driven, and the first image and the second light source unit are driven. The observation device according to (19), wherein the normal observation image is obtained by combining the image and the image.
(21) In the normal observation mode, the normal observation image is generated by adding together the RGB values of the first image and the RGB values of the second image, the observation according to (20). apparatus.
(22) In the special observation mode in which a fluorescence observation image of the operative field is obtained by the excitation light, only the second light source unit of the first light source unit and the second light source unit is driven, and the second light source unit is driven. The observation device according to any one of (19) to (21), in which two images are obtained as the fluorescence observation image.
(23) In the normal/special observation mode in which the normal observation image of the surgical field by the broadband light and the fluorescence observation image of the surgical field by the excitation light are simultaneously obtained, the first light source unit and the second light source unit are used. The light source unit is driven together, and the first image and the second image are combined to obtain an image in which the normal observation image and the fluorescence observation image are superimposed, (19) to The observation device according to any one of (21).
(24) In the normal/special observation mode, the R value of the first image and the GB value of the second image are added together, so that the normal observation image and the fluorescence observation image are superimposed. The observation device according to (23), wherein an image is generated.
(25) The short wavelength band image generation unit generates the second image based on light in which a wavelength band component corresponding to the excitation light is attenuated or removed, and in the normal/special observation mode, The image in which the normal observation image and the fluorescence observation image are superimposed is generated by adding up the RGB value of the first image and the RGB value of the second image, (23). Observation device.

1 Endoscope Device 2 Microscope Device 10, 20, 30, 40, 1100, 2100 Illumination Device 101 First Light Source Unit 103, 103a First Collimating Optical System 105 Coupling Optical System 107 Optical Fiber 109 Third Collimating Optical System 111 Diffusing member 113, 113a Second collimating optical system 115, 115b Dichroic mirror 117, 117a Condenser optical system 119 Third light source unit 120, 120b Second light source unit 121R, 121G, 121B Laser light source 122R, 122G, 122B Dichroic Mirror 125 Second dichroic mirror 130 Light guide 1101 Laser line filter 1103, 1107 Half mirror 1105, 1109 Photodetector 1111 Projection lens 1120 Control unit 1121 First light source unit drive control unit 1123 Second light source unit drive control unit 1200, 1200c Endoscope section 1210 Lens barrel 1220, 1220c, 2200 Imaging unit 1221 Optical filter 1223 First imaging element 1225 Second imaging element 1227 Second optical filter 1300 Image processing apparatus 1301 Long wavelength band Image generation section 1303 Short wavelength band Image generation unit 1305 Observation image generation unit 1307 Input unit 1400 Display device 1500 Observation site 1501 First irradiation range 1503 Second irradiation range 2227 Image lens

Claims (19)

A first light source unit that emits white light;
A second light source unit that emits laser light in a plurality of predetermined wavelength bands included in the wavelength band of the white light;
A diffusing member that generates a secondary light source by diffusing the laser light emitted from the second light source unit;
A dichroic mirror that multiplexes white light emitted from the first light source unit and laser light emitted from the secondary light source;
Equipped with
The dichroic mirror attenuates a component of a wavelength band corresponding to the laser light in the white light, and combines the laser light with the white light in which a component of a wavelength band corresponding to the laser light is attenuated. Lighting equipment. A first collimating optical system that converts white light emitted from the first light source unit into substantially parallel light;
A second collimating optical system that converts the laser light emitted from the diffusing member into substantially parallel light;
Further equipped with,
The dichroic mirror multiplexes white light converted into substantially parallel light by the first collimating optical system and laser light converted into substantially parallel light by the second collimating optical system.
The lighting device according to claim 1. A coupling optical system for coupling the laser light emitted from the second light source unit to an optical fiber;
A third collimating optical system for converting the laser light emitted from the optical fiber into substantially parallel light;
Further equipped with,
The diffusing member diffuses the laser light emitted from the third collimating optical system to generate a secondary light source.
The lighting device according to claim 2. Further comprising a condenser optical system for forming an image of the light multiplexed by the dichroic mirror on the incident end of the light guide,
The condenser optical system outputs the light from the secondary light source so that the size of the image of the secondary light source formed at the light incident end of the light guide is substantially the same as the diameter of the light guide incident end. Image the light at the entrance end of the light guide,
The lighting device according to claim 1. The second light source unit has a plurality of laser light sources,
The plurality of laser light sources include at least a red laser light source that emits a red laser light, a green laser light source that emits a green laser light, and a blue laser light source that emits a blue laser light,
The lighting device according to claim 1. The second light source unit has a plurality of laser light sources,
By independently controlling the driving of the plurality of laser light sources, the color temperature of the light combined by the dichroic mirror is adjusted.
The lighting device according to claim 5. At least one of the laser light sources forming the second light source unit emits laser light in a wavelength band corresponding to excitation light used for fluorescence observation of an observation site,
The lighting device according to claim 1. A third light source unit that emits light in a wavelength band different from the laser light emitted from the second light source unit,
Light obtained by combining the white light emitted from the first light source unit and the light emitted from the third light source unit enters the dichroic mirror,
The dichroic mirror combines the white light emitted from the first light source unit with the light emitted from the third light source unit, and the laser light emitted from the second light source unit. And are further combined,
The lighting device according to claim 1. The first light source unit and the third light source unit are configured by LEDs.
The lighting device according to claim 8. Emitting white light from the first light source unit,
Emitting laser light of a plurality of predetermined wavelength bands included in the wavelength band of the white light from the second light source unit;
Generating a secondary light source by diffusing the laser light emitted from the second light source unit by the diffusing member;
Combining the white light emitted from the first light source unit and the laser light emitted from the secondary light source by a dichroic mirror;
Including
The dichroic mirror attenuates a component of a wavelength band corresponding to the laser light in the white light, and combines the laser light with the white light in which a component of a wavelength band corresponding to the laser light is attenuated. To do
Lighting method. An illumination device that outputs at least one of white light and excitation light with which the surgical field of a patient is irradiated,
The lighting device is
A first light source unit that emits white light;
A second light source unit that emits laser light in a plurality of predetermined wavelength bands including a wavelength band corresponding to the excitation light, which is included in the wavelength band of the white light;
A diffusing member that generates a secondary light source by diffusing the laser light emitted from the second light source unit;
A dichroic mirror that multiplexes white light emitted from the first light source unit and laser light emitted from the secondary light source;
Equipped with
The dichroic mirror attenuates a component of a wavelength band corresponding to the laser light in the white light, and combines the laser light with the white light in which a component of a wavelength band corresponding to the laser light is attenuated. To do
Observation device. The observation device further includes a lens barrel that is inserted into a body cavity of a patient, the output light from the illumination device is guided inside, and the operation field in the body cavity is irradiated with the output light. , Is an endoscopic device,
The observation device according to claim 11. A long-wavelength band image generation unit that generates a first image based on light having a wavelength band longer than the excitation light and including a wavelength band of fluorescence due to the excitation light;
A short wavelength band image generation unit that generates a second image based on light having a wavelength band shorter than the fluorescence and including the wavelength band of the excitation light;
Is further provided,
The observation device according to claim 11. In the normal observation mode where you can get a normal observation image of the operative field with white light,
The first light source unit and the second light source unit are both driven,
The normal observation image is obtained by combining the first image and the second image,
The observation device according to claim 13. In the normal observation mode, the normal observation image is generated by adding the RGB values of the first image and the RGB values of the second image,
The observation device according to claim 14. In the special observation mode where a fluorescence observation image of the surgical field with excitation light can be obtained,
Of the first light source unit and the second light source unit, only the second light source unit is driven,
The second image is obtained as the fluorescence observation image,
The observation device according to claim 13. In the normal/special observation mode in which a normal observation image of the surgical field with white light and a fluorescence observation image of the surgical field with excitation light are obtained simultaneously,
The first light source unit and the second light source unit are both driven,
By synthesizing the first image and the second image, an image in which the normal observation image and the fluorescence observation image are superimposed is obtained.
The observation device according to claim 13. In the normal/special observation mode, the R value of the first image and the GB value of the second image are added together to generate an image in which the normal observation image and the fluorescence observation image are superimposed. Will be
The observation device according to claim 17. The short wavelength band image generation unit generates the second image based on light in which a component of a wavelength band corresponding to the excitation light is attenuated or removed,
In the normal/special observation mode, the RGB values of the first image and the RGB values of the second image are added together to generate an image in which the normal observation image and the fluorescence observation image are superimposed. Will be
The observation device according to claim 17.