JP6450492B1 - Endoscopic illumination device and endoscope system - Google Patents

Abstract

An object of the present invention is to support the imaging of visible light and fluorescence in an endoscope while suppressing an increase in diameter of an insertion portion.
In an endoscope illumination device, irradiation is performed from each of a first light source, a second light source that outputs light having a wavelength different from the light emitted from the first light source, and the first light source and the second light source. The wavelength characteristics emitted from each of the optical multiplexing means for guiding the light having different wavelength characteristics to the same light guide member, the insertion portion for inserting the light guide member, and the first light source and the second light source An optical element provided in an optical path through which different lights are combined and propagated, wavelength-converting at least part of the light emitted from the first light source, and transmitting at least part of the light emitted from the second light source; , Provided.
[Selection] Figure 2

Description

  The present disclosure relates to an endoscope illumination device and an endoscope system.

  Conventionally, for example, a fluorescent observation device is known that administers a fluorescent agent to a lesion, excites the fluorescent agent with infrared light to generate fluorescence, and obtains a fluorescent observation image with high brightness (see, for example, Patent Document 1). ). This fluorescence observation apparatus includes a light guide that propagates excitation light incident from an excitation light source to the tip, and a line light guide that propagates reference light incident from a reference light source as line-shaped light in a body cavity. Thread through the insertion section. That is, the fluorescence observation apparatus guides a plurality of illumination lights through the respective optical fibers, and performs diffusion irradiation with the respective diffusion lenses provided at the light emitting ends.

JP 2008-229025 A

  However, in the configuration of Patent Document 1, when imaging with visible light and fluorescence is performed, if a plurality of optical fibers and diffusion lenses corresponding to the respective light sources are arranged in the insertion portion, the insertion portion and the distal end of the endoscope are outside. There was a problem that the diameter size was increased, and it was difficult to suppress an increase in the diameter of the insertion portion.

  The present disclosure has been devised in view of the above-described conventional circumstances, and suppresses an increase in the diameter of the insertion portion, and can be used to support imaging of visible light and fluorescence in an endoscope. And it aims at providing an endoscope system.

The present disclosure includes a first light source, a second light source that outputs light having a wavelength including an infrared region for exciting a fluorescent substance, which is different from the light emitted from the first light source, the first light source, and the light source Optical multiplexing means for guiding light emitted from each of the second light sources and having different wavelength characteristics to the same light guide member, an insertion portion for inserting the light guide member, the first light source, and the second light source Provided in an optical path through which light having different wavelength characteristics irradiated from each of the light sources is combined, propagates at least part of the light emitted from the first light source, and irradiates from the second light source An endoscope illumination device comprising: an optical element that transmits at least part of the light to be transmitted.

  Further, the present disclosure provides an endoscope illumination device, a camera unit provided at a distal end of the insertion unit, and a captured image signal based on an imaging signal of an affected area of the subject imaged by the camera unit to a monitor An endoscope system is provided.

  According to the present disclosure, it is possible to suppress an increase in diameter of the insertion portion, and it is possible to support imaging of visible light and fluorescence in an endoscope.

The perspective view which shows the example of an external appearance of the endoscope system which concerns on Embodiment 1. FIG. The block diagram which shows the internal structural example of the endoscope system shown in FIG. Schematic when a prism is placed at the tip and a phosphor is placed at the exit Perspective view of optical deflector for camera and illumination device Camera operation diagram Schematic diagram of an optical deflector according to a modification provided with a transmissive phosphor Schematic diagram of an optical deflector according to a modification provided with a reflective phosphor The figure explaining the flow which irradiates a subject with excitation light, makes it emit fluorescence, and receives fluorescence from a subject Graph showing characteristics of excitation light, ICG fluorescence and excitation light cut filter Timing chart showing an example of IR excitation light exposure and visible light exposure in an endoscope system Schematic diagram showing an example of images in the simultaneous output mode displayed on the monitor Schematic diagram showing an example of the image in the superimposed output mode displayed on the monitor The block diagram which shows the modification of the internal structure of the illuminating device for endoscopes

  Hereinafter, an embodiment that specifically discloses an endoscope illumination apparatus and an endoscope system according to the present disclosure will be described in detail with reference to the drawings as appropriate. However, more detailed description than necessary may be omitted. For example, detailed descriptions of already well-known matters and repeated descriptions for substantially the same configuration may be omitted. This is to avoid the following description from becoming unnecessarily redundant and to facilitate understanding by those skilled in the art. The accompanying drawings and the following description are provided to enable those skilled in the art to fully understand the present disclosure, and are not intended to limit the claimed subject matter.

  FIG. 1 is a perspective view showing an example of the appearance of an endoscope system 11 according to the first embodiment. The endoscope system 11 includes a camera controller 13, a monitor 15, an endoscope illumination device 17, and an endoscope unit 19.

  The camera controller 13 includes an image processor 63 and a light source driving circuit 65 described later (see FIGS. 2 and 8). The camera controller 13 causes the image processor 63 to display a captured image (still image or moving image) obtained by the camera 21 (an example of the camera unit) capturing an observation target (for example, the subject or an affected part in the subject). To process. The camera controller 13 performs image processing on the captured image input from the camera 21 via the transmission cable 23 and generates a captured image after the image processing. The image processing is predetermined image processing, and includes, for example, color correction, gradation correction, and gain adjustment.

  The camera controller 13 is connected to a first excitation light source 25 (an example of a first light source) and a second excitation light source 27 (an example of a second light source) via a light source drive cable 14. The camera controller 13 generates a control signal for driving the first excitation light source 25 in the light source driving circuit 65 via the light source driving cable 14 and outputs the control signal to the first excitation light source 25. In addition, the camera controller 13 generates a control signal for driving the second excitation light source 27 in the light source driving circuit 65 via the light source driving cable 14 and outputs the control signal to the second excitation light source 27.

  The monitor 15 displays the captured image output from the camera controller 13. The monitor 15 includes a display device such as an LCD (Liquid Crystal Display) or a CRT (Cathode Ray Tube). In the endoscope system 11 according to the first embodiment, the monitor 15 includes a visible light image captured based on the irradiated visible light and a fluorescent image captured based on the fluorescence generated by the irradiated excitation light. Is displayed (see FIG. 11 or FIG. 12 described later).

  FIG. 2 is a block diagram illustrating an internal configuration example of the endoscope system 11 illustrated in FIG. 1. The endoscope system 11 includes an endoscope illumination device 17. The endoscope illumination device 17 includes a first excitation light source 25 (an example of a first light source), a second excitation light source 27 (an example of a second light source), and a multiplexing prism 35 (an example of an optical multiplexing unit). The optical fiber 29 (an example of a light guide member), the insertion portion 31, and the phosphor 33 are included as main constituent members.

  The first excitation light source 25 is configured using, for example, a semiconductor laser such as a laser diode capable of emitting laser light having a half width of about 1/10 compared to light from an LED (Light Emission Diode). . The first excitation light source 25 excites the phosphor 33 to generate pseudo white light (that is, normal RGB visible light) in a narrow-band blue region (for example, in a wavelength band of 380 to 450 nm). Light having a wavelength).

  The second excitation light source 27 is configured using, for example, a semiconductor laser such as a laser diode (Laser Diode) capable of emitting laser light having a half-value width of about 1/10 compared to light from an LED (Light Emission Diode). . The second excitation light source 27 irradiates and outputs light in a narrow wavelength band different from the wavelength band of light emitted from the first excitation light source 25. That is, the second excitation light source 27 is light in an infrared region (for example, a wavelength band of 690 to 820 nm) for exciting a fluorescent agent that is administered in advance to an affected area of a subject before endoscopic surgery or endoscopy. (With light having a wavelength of 1).

  The optical multiplexing means guides the light emitted from the first excitation light source 25 and the light emitted from the second excitation light source 27 to the same optical fiber 29, respectively. In the first embodiment, the optical multiplexing means is a multiplexing optical member (for example, a multiplexing prism 35) that multiplexes (that is, combines) blue light and infrared light. The multiplexing prism 35 is configured using, for example, a blue side input prism 37 and an infrared side input prism 39. The multiplexing prism 35 guides blue light from the first excitation light source 25 and infrared light from the second excitation light source 27 to the same optical fiber 29 via the condenser lens 41. You may form with one member which can be lighted. For example, a multiplexing optical member is configured by an integrated prism in which a filter that reflects light in a blue region and passes light in an infrared region is disposed on an opposing surface where two triangular prisms having the same shape are in contact with each other. May be.

  The endoscope illumination device 17 causes blue region light and infrared region light multiplexed by the multiplexing prism 35 to enter from the light incident end of the optical fiber 29. A condensing lens 41 is provided between the multiplexing prism 35 and the optical fiber 29.

  The first excitation light source 25, the second excitation light source 27, the multiplexing prism 35, and the condenser lens 41 constitute an illumination unit 43.

  The optical fiber 29 can be a single optical fiber, for example. The optical fiber 29 may be a bundle fiber in which a plurality of optical fiber strands are bundled. Since the endoscope illumination device 17 may use a single optical fiber or bundle fiber, there is no need to arrange a plurality of optical fibers 29 and diffusion lenses corresponding to each light source in the insertion portion 31. Thereby, in the endoscope part 19, the diameter reduction of the insertion part 31 can be achieved.

  The insertion unit 31 passes through the optical fiber 29. In addition, the transmission cable 23 is inserted through the insertion portion 31. The insertion part 31 becomes an insertion part of the endoscope part 19 inserted into the body cavity of the subject, for example. In Embodiment 1, the insertion part 31 becomes a cylindrical rigid member. The insertion portion 31 is a flexible tube-like soft member when the endoscope portion 19 is a flexible mirror.

  An imaging window is disposed on the distal end surface of the insertion portion 31. The imaging window is formed including an optical material such as optical glass or optical plastic, and allows light from a subject (for example, a subject or an affected part in the subject) to enter. An illumination window is disposed on the distal end surface of the insertion portion 31. The illumination window is formed including an optical material such as optical glass or optical plastic, and emits illumination light from the light exit end of the optical fiber 29. In the first embodiment, the illumination light is emitted from an optical deflector (see later) provided at the light emission end of the optical fiber 29.

  FIG. 3 is an enlarged view of a main part of the endoscope illumination device 17 shown in FIG. The phosphor 33 is provided in an optical path through which the lights of the first excitation light source 25 and the second excitation light source 27 are combined and propagated. In the first embodiment, the phosphor 33 is provided, for example, at a light emitting end of an optical deflector (see later). The phosphor 33 is excited by the light of the first excitation light source 25 and emits fluorescence. That is, the first excitation light source 25 emits light in the wavelength band of the blue region and is superimposed on the fluorescence of the phosphor 33 (see later), so that pseudo white light (that is, normal RGB light) is generated. Irradiation is directed toward the affected area in the subject. Therefore, the phosphor 33 according to Embodiment 1 is for white light generation. In addition, the phosphor 33 transmits the light from the second excitation light source 27.

  Specifically, in the case of the white specification, the phosphor 33 is, for example, a yellow phosphor. By this phosphor 33, part of the blue region light from the optical fiber 29 is wavelength-converted into yellow light, and these lights are mixed to generate pseudo white light. At this time, most of the light in the infrared region passes through the phosphor 33 as it is. Some of these white light and infrared light are refracted and reflected by the phosphor fine particles and diffused.

  The phosphor 33 is disposed at the light incident end or the light emitting end of the optical fiber 29. In the first embodiment, an optical deflector 45 may be provided between the light emitting end of the optical fiber 29 and the phosphor 33. That is, the light emitted from the light emitting end of the optical fiber 29 is emitted through the phosphor 33 provided at the light emitting end of the optical deflector 45.

  The optical deflector 45 includes a first prism 47 and a second prism 49. The first prism 47 is connected to the optical fiber 29 and allows light from the light exit end of the optical fiber 29 to enter. The first prism 47 is fixed inside the insertion portion 31 and connected to the optical fiber 29. On the other hand, the second prism 49 is rotated integrally with a camera (an example of a camera unit) 21 that is rotatably supported at the distal end of the insertion unit 31. The second prism 49 deflects the light incident from the first prism 47 and irradiates the subject. Since the endoscope illumination device 17 includes the optical deflector 45 between the optical fiber 29 and the camera 21, the direction of the illumination light can be changed over a wide range without increasing the diameter of the insertion portion 31. . The phosphor 33 is provided at the light emitting end of the second prism 49.

  FIG. 4 is a perspective view of the camera 21 and the light deflector 45 for the illumination device. In the camera 21, a lens barrel holder 53 is rotatably supported around a rotation shaft 51 orthogonal to the axis of the insertion portion 31 inside the insertion portion 31. The second prism 49 is fixed to the lens barrel holder 53 and thereby rotated integrally with the camera 21.

  FIG. 5 is an explanatory diagram of the operation of the camera 21. The camera 21 is configured to include a lens 55 and an image sensor 57. The imaging element 57 is a solid-state imaging element such as a CCD (Charge Coupled Device) or a CMOS (Complementary Metal Oxide Semiconductor). The image sensor 57 is, for example, a single-plate image sensor that can simultaneously receive and image infrared light, red light, blue light, and green light.

  The camera 21 can rotate at a rotation angle of 0 to 90 degrees with the rotation axis 51 as the center and the direction of the optical axis of the lens 55 as a reference at the distal end of the insertion portion 31. As a result, when the insertion unit 31 is inserted into the body cavity of the subject, the camera 21 enables imaging at a wide angle from the front surface to the inner wall of the body cavity. At that time, the endoscope illumination device 17 can irradiate illumination light accurately and widely to the imaging region by rotating the second prism 49 of the optical deflector 45 integrally with the camera 21.

  The camera 21 is connected to the camera controller 13 via the transmission cable 23. The camera 21 can transmit and receive power and various signals (for example, an imaging signal and a control signal) to and from the camera controller 13 via the transmission cable 23. For example, the imaging signal is output from the imaging device 57 provided in the camera 21 and transmitted to the camera controller 13 via the transmission cable 23.

  The camera 21 includes an IR (Infrared Radiation) excitation light cut filter 59 (see FIG. 8) in the optical path of the imaging optical system including one or a plurality of lenses. The IR excitation light cut filter 59 is provided between the lens 55 and the image sensor 57, for example. The IR excitation light cut filter 59 cuts by reflecting or absorbing at least a part of the excitation light irradiated and reflected on the subject out of the light from the subject. The IR excitation light cut filter 59 transmits light having a wavelength of, for example, 690 nm to 820 nm so that the wavelength corresponding to the light emitted from the second excitation light source (IR band excitation light) can be accurately cut (blocked). Shut off.

  FIG. 6 is a schematic diagram of an optical deflector 45 according to a modification in which a transmissive phosphor is provided. The phosphor 33 may be provided in addition to the light emitting end of the light deflector 45. That is, the phosphor 33 may be provided between the first prism 47 and the second prism 49.

  FIG. 7 is a schematic diagram of an optical deflector 45 according to a modification in which a reflective phosphor is provided. Further, the phosphor 33 may be a reflective phosphor. The reflective phosphor can be provided on the reflection surface of the second prism 49. In this case, it is more desirable that the reflection type phosphor is provided with the reflection plate 61 on the surface opposite to the reflection surface of the second prism 49. The reflective phosphor is advantageous in heat countermeasures compared to the transmissive phosphor 33.

  FIG. 8 is a diagram for explaining the flow of receiving fluorescence by irradiating a subject with excitation light to emit fluorescence. Prior to surgery or examination, for example, indocyanine green (ICG), which is a fluorescent drug, is preliminarily administered to the affected part TG of the subject that is the affected part. When observing fluorescence generated by irradiating the affected area with IR band excitation light (so-called fluorescence observation), near-infrared light (as described above) is applied to a site such as a tumor where indocyanine green is excessively accumulated (ie, the affected area). IR excitation light) is irradiated. As a result, the fluorescent agent is excited by the excitation light and emits fluorescence, so that the affected part where the fluorescent agent such as ICG is accumulated or its surroundings emits fluorescence, and the site including the affected part can be imaged. When excited by near infrared light (for example, having a wavelength in the wavelength band of 690 to 820 nm), the ICG emits fluorescence by longer wavelength near infrared light (for example, peak wavelength 835 nm).

  The camera controller 13 includes an image processor 63 and a light source driving circuit 65. The image processor 63 performs image processing on the fluorescence emission image and the visible light image that are alternately output from the image sensor 57 in a time division manner, and outputs the captured image after the image processing to the monitor 15. The light source driving circuit 65 drives the first excitation light source 25, emits light in the blue region, and artificially emits white light (that is, normal RGB light) in the subject through the fluorescent light emission of the phosphor 33. Can irradiate the affected area. The light source driving circuit 65 can drive the second excitation light source 27 to irradiate the affected part in the subject with IR excitation light.

  Here, blue light having a wavelength in a wavelength band of, for example, 380 nm to 450 nm of the first excitation light source 25, pseudo white light generated by exciting the phosphor 33 with the blue light, and the second excitation light source 27, for example, a case where excitation light (IR light) having a wavelength in a wavelength band of 690 nm to 820 nm is irradiated toward the affected area TG, respectively. In addition, as long as excitation light having a wavelength of, for example, 780 nm or 808 nm is used in the wavelength band of 690 nm to 820 nm and included in the wavelength band of excitation light suitable for fluorescence emission, excitation light having other wavelengths is used. Also good. Further, three or more excitation lights may be used.

  Visible light (that is, the above-described white light) is reflected by the affected part TG and is received by the image sensor 57 through the IR excitation light cut filter 59. As described above, the IR excitation light cut filter 59 blocks transmission of light having a wavelength of 690 nm to 820 nm. Therefore, the visible light reflected by the affected part TG is received by the image sensor 57 only by partially cutting light in a band of 690 nm to 700 nm, for example.

  On the other hand, when the ICG used in Embodiment 1 is excited with IR excitation light, it emits fluorescence with light having a wavelength of 830 nm to 900 nm (for example, 830 nm). The IR light from the affected part TG includes excitation light reflected by the subject (for example, excitation light having a wavelength having a wavelength band of 690 nm to 820 nm) and fluorescence emitted from the subject (830 nm to 900 nm). When transmitted through the IR excitation light cut filter 59, transmission of light having a wavelength of 690 nm to 820 nm is blocked in the IR light, and fluorescence having a wavelength of 830 nm to 900 nm is received by the image sensor 57.

  FIG. 9 is a graph showing the characteristics of the excitation light, ICG fluorescence, and IR excitation light cut filter 59. The IR excitation light cut filter 59 is an edge filter having a steep boundary 67 (edge) and boundary 69 between a transmission band and a blocking band (in other words, a transmission prohibition band). What is required of this type of edge filter is that the change from the stop band to the transmission band is generally as sharp as possible and the transmission band is as close to 100% as possible. In the IR excitation light cut filter 59 according to Embodiment 1, the wavelength of the excitation light (refer to the alternate long and short dash line in FIG. 9) is at the approximate center of the stop band. Fluorescence due to the excitation light (that is, ICG fluorescence, see the broken line in FIG. 9) is as weak as several percent with respect to the excitation light. This is particularly the case when indocyanine green (ICG), a medical fluorescent agent that is harmless to the human body, is administered into the body of the subject, and the affected area is irradiated with near infrared light to illuminate the affected area. It corresponds to. Therefore, the image processor 63 (see FIG. 8) adjusts the gain so as to increase the gain of the fluorescence emission image. For this reason, image quality deteriorates even when weak excitation light enters. For these reasons, it is preferable to ensure a sufficient range for the stopband with respect to the wavelength of the excitation light.

  On the other hand, the ICG fluorescence due to the excitation light peaks in a gentle wavelength range continuously in the wavelength band of the excitation light. Therefore, the boundary 69 between the stop band and the transmission band of the IR excitation light cut filter 59 is important. That is, there is a demand for capturing the wavelength Wk of the ICG fluorescence as much as possible while separating the boundary 69 from the wavelength of the excitation light. The IR excitation light cut filter 59 is particularly weak in the ICG fluorescence wavelength Wk, and is cut off by including a wavelength region close to the excitation light in the stop band. This makes it possible to efficiently capture an effective effective fluorescence wavelength Wka out of the weak fluorescence wavelength Wk while suppressing the penetration of excitation light as much as possible.

  FIG. 10 is a timing chart showing an example of IR excitation light exposure and visible light exposure in the endoscope system 11. In the endoscope system 11, the light source driving circuit 65 of the camera controller 13 performs control to alternately output the light from the first excitation light source 25 and the light from the second excitation light source 27. The camera controller 13 acquires a fluorescence image at the irradiation timing by the light of the second excitation light source 27 at an imaging timing that does not overlap with the irradiation timing by the light of the first excitation light source 25.

  The endoscope system 11 starts an imaging operation by receiving an operation of turning on a switch (not shown) provided in the camera controller 13 or the endoscope unit 19, for example. When the imaging operation is started, the camera controller 13 drives the light source driving circuit 65.

  When the second excitation light source 27 emits IR excitation light, the IR excitation light is irradiated toward the subject through the optical fiber 29 of the insertion portion 31, and illuminates the surroundings including the affected area. Light from a subject such as an affected part is collected by the lens 55. Of the light from the subject such as the affected part, the IR excitation light reflected by the subject is blocked by the IR excitation light cut filter 59, but the drug fluorescence emitted by the subject passes through the IR excitation light cut filter 59. Thus, an image is formed on the imaging surface of the image sensor 57.

  In the affected area (a part of the subject) irradiated with the IR excitation light, fluorescence emission occurs so that the peak light amount is obtained after a predetermined time (for example, several msec) from the irradiation of the IR excitation light, and the drug fluorescence is output. . Irradiation with IR excitation light is started at least a predetermined time before the start of exposure so that exposure is started after the drug fluorescence output from the subject reaches the peak light amount.

  The camera controller 13 turns off the electronic shutter of the image sensor 57 after a predetermined time has elapsed from the start of exposure, and ends the exposure by fluorescence emission from the subject. When the reading of the IR fluorescence signal by the image processor 63 is completed, the camera controller 13 outputs a captured image signal obtained from the IR fluorescence signal to the monitor 15. The monitor 15 displays the fluorescence emission image for a period until the fluorescence emission image is switched to the visible light image.

  When the reading of the IR fluorescence signal by the image processor 63 is completed, the camera controller 13 drives the light source driving circuit 65 to turn on visible light. The light source driving circuit 65 turns on the first excitation light source 25 and lights visible light.

  When the first excitation light source 25 is turned on to emit visible light, the visible light is irradiated toward the subject through the optical fiber 29 of the insertion portion 31 to illuminate the surroundings including the affected part. Visible light reflected by the affected part or the like is collected by the lens 55, passes through the IR excitation light cut filter 59, and forms an image on the imaging surface of the imaging element 57.

  When the reading of the IR fluorescence signal by the image processor 63 is completed, the camera controller 13 outputs a sensor reset signal to the image sensor 57 to return the image sensor 57 to the state before the exposure start. After the sensor reset, the camera controller 13 turns on the electronic shutter of the image sensor 57 and starts exposure with visible light.

  Simultaneously with the completion of the visible light exposure, the image processor 63 starts reading a visible light signal from the image sensor 57. The visible light signal is a signal obtained by exposure to visible light. The reading of the visible light signal ends after the reading time corresponding to the number of pixels has elapsed. When the reading of the visible light signal by the image processor 63 is completed, the camera controller 13 outputs a captured image signal of a visible light image obtained from the visible light signal to the monitor 15. The monitor 15 displays the visible light image for a period until the visible light image is switched to the fluorescent light emission image.

  The endoscope system 11 performs an imaging operation over an imaging period. During this time, the fluorescence emission image and the visible light image are displayed in contrast or superimposed on the same area of the monitor 15. In addition, since the switching of the display between the fluorescence emission image and the visible light image is short, it can be said that the fluorescence emission image and the visible light image are displayed in an overlapping manner.

  For example, the user turns off a switch (not shown) provided in the camera controller 13 or the endoscope unit 19. When the imaging is completed, the camera controller 13 outputs a signal for ending the photoelectric conversion by the imaging element 57, and ends the imaging operation. The light source drive circuit 65 turns off the first excitation light source 25 and the second excitation light source 27 and ends the illumination operation.

  FIG. 11 is a schematic diagram illustrating an image example displayed in the simultaneous output mode displayed on the monitor 15. The endoscope system 11 outputs a captured image signal based on either the simultaneous output mode or the superimposed output mode.

  In the simultaneous output mode, the camera controller 13 has a visible light image (that is, an RGB image G1) acquired by illumination of light from the first excitation light source 25 and a fluorescence image (that is, acquired by illumination of light from the second excitation light source 27). , IR image G2) and the like are displayed on the monitor 15. The visible light image (that is, the RGB image G1) is an image in which normal RGB light (white light) is irradiated to visually determine not only the affected part TG but also the tissue structure around the affected part TG. It has become. On the other hand, in the fluorescence image (that is, IR image G2), white appears in the affected area TG in which fluorescent drugs such as ICG are accumulated, and black in other areas excluding the affected area TG. That is, according to the IR image G2, the state of the affected part TG can be clearly determined. In the simultaneous output mode, the monitor display unit 71 displays the RGB image G1 and the IR image G2 on different screens.

  FIG. 12 is a schematic diagram illustrating an example of an image in the superimposed output mode displayed on the monitor 15. In the superimposed output mode, the fluorescence image (that is, the RGB image G <b> 1) acquired by the camera controller 13 with the illumination of the light from the first excitation light source 25 is added to the visible light image (that is, the RGB image G <b> 1). , The image (that is, the composite image GZ) on which the IR image G2) is superimposed is displayed on the monitor 15. In the superimposition output mode, the monitor display unit 71 displays a composite image GZ in which the RGB image G1 and the IR image G2 are superimposed on one screen.

  Next, the operation of each part in the endoscope system 11 according to the first embodiment will be described.

  The endoscope illumination device 17 according to Embodiment 1 includes a first excitation light source 25 (an example of a first light source) and second excitation that outputs light having a wavelength different from the light emitted from the first excitation light source 25. Light having different wavelength characteristics (for example, wavelength bands) emitted from the light source 27 (an example of the second light source), the first excitation light source 25, and the second excitation light source 27 is the same optical fiber 29 (light guide). And an optical multiplexing means for guiding light to an example of a member. The endoscope illuminating device 17 is provided in an optical path through which light from the insertion portion 31 through which the optical fiber 29 is inserted and the light from the first excitation light source 25 and the second excitation light source 27 are combined and propagated. An optical element (for example, a phosphor 33) that converts the wavelength of at least part of the light emitted from the light source 25 and transmits at least part of the light of the second excitation light source 27. Here, the phosphor 33 transmits at least a part of the light of the second excitation light source 27. For example, a part of the light is absorbed by the phosphor 33, and a part of the light constitutes the phosphor 33. This is because the particles to be diffused (that is, transmitted) by refraction or reflection. Further, the optical element is not limited to the above-described phosphor 33. For example, wavelength conversion is possible as long as light can be emitted by the light from the first excitation light source 25 and at least part of the light from the second excitation light source 27 can be transmitted. It may be a non-linear crystal.

  In the endoscope illuminating device 17 according to the first embodiment, light of different wavelengths output from the first excitation light source 25 and the second excitation light source 27 are combined by the optical multiplexing means, and the same optical path is configured. It is guided to the optical fiber 29. The optical fiber 29 that guides the combined light is inserted into the insertion portion 31 in the endoscope portion 19 and extends from the proximal end of the insertion portion 31 to the distal end. Therefore, the endoscope illuminating device 17 does not need to arrange a plurality of optical fibers 29 and diffusion lenses corresponding to the respective light sources in the insertion portion 31 as in the conventional structure. That is, space saving can be achieved. As a result, it is possible to capture visible light and fluorescence while reducing the diameter of the insertion portion 31 and the distal end of the endoscope while suppressing the increase in the diameter of the insertion portion 31 as much as the optical fiber 29 and the diffusion lens can be reduced. .

  Therefore, according to the endoscope illumination device 17 according to the first embodiment, the increase in the diameter of the insertion portion 31 is suppressed, and support for imaging visible light and fluorescence in the endoscope portion 19 is effectively provided. It can be carried out.

  In the endoscope illumination device 17, the phosphor 33 is disposed at the light incident end or the light emitting end of the optical fiber 29, for example, for generating white light. The first excitation light source 25 irradiates (outputs) blue region light for generating pseudo white light by exciting the phosphor 33 to emit fluorescence. The second excitation light source 27 irradiates (outputs) infrared light for exciting a fluorescent agent that is administered to the subject in advance. The optical multiplexing means is optical means for multiplexing (for example, a multiplexing prism 35) that multiplexes light in the blue region and light in the infrared region. The phosphor 33 is not limited to white light generation as long as it can be excited by light from the first excitation light source 25 to generate fluorescence and transmit at least part of the light from the second excitation light source 27.

  In the endoscope illumination device 17, the phosphor 33 is for white light generation. The blue light output from the first excitation light source 25 is guided to the optical fiber 29 through the multiplexing prism 35. When the blue light propagated through the optical fiber 29 is emitted from the light emitting end of the optical fiber 29, the phosphor 33 generates pseudo white light (light in which the light in the blue region and the fluorescence are superimposed). Is irradiated into the subject. The infrared light output from the second excitation light source 27 is also guided to the optical fiber 29 through the multiplexing prism 35. The infrared light propagated through the optical fiber 29 is transmitted through the phosphor 33 from the light emitting end of the optical fiber 29 and emitted. Infrared light transmitted through the phosphor 33 is irradiated into the subject, and excites a fluorescent agent such as ICG administered in advance to generate fluorescence. Note that blue light and infrared light are emitted including diffused light that diffuses by being diffusely reflected by the fine particles in the phosphor 33 when irradiated as illumination light through the phosphor 33.

  In the endoscope illumination device 17, the first excitation light source 25 and the second excitation light source 27 are each configured using a semiconductor laser.

  In the endoscope illumination device 17, the light in the blue region irradiated from the first excitation light source 25 and the light in the infrared region irradiated from the second excitation light source 27 each have a narrow wavelength band. High strength. Therefore, the endoscope illumination device 17 can irradiate appropriate and pseudo white light by causing the blue region light emitted from the first excitation light source 25 to excite the phosphor 33 to generate yellow light. is there. In addition, since the illumination device 17 for endoscope 17 has a narrow band of light in the infrared region irradiated from the second excitation light source 27, it is possible to irradiate excitation light suitable for excitation of a fluorescent agent such as ICG.

  In the endoscope illumination device 17, the optical fiber 29 has a circular cross-sectional shape orthogonal to the direction of the axis, and the outer diameter is 5 mm or less.

  In this endoscope illuminating device 17, the maximum outer diameter of the optical fiber 29 can be realized at 5 mm or less from the manufacturable lower limit value, so that it corresponds to each of the first excitation light source 25 and the second excitation light source 27. There is no need to arrange the plurality of optical fibers 29 and the diffusion lens in the insertion portion 31. Thereby, the diameter reduction of the insertion part 31 can be achieved.

In the endoscope illumination device 17, the optical fiber 29 has a cross-sectional area of, for example, 80 mm ² or less, which is a cross-sectional shape orthogonal to the axial direction (for example, circular, but not limited to a circular shape).

In this endoscope illumination device 17, if the cross-sectional area of the cross-sectional shape of the optical fiber 29 orthogonal to the direction of the axis of the insertion portion 31 falls within the range of 80 mm ² or less from the lower limit that can be manufactured, the cross-sectional shape is circular. It is not limited to. Accordingly, the insertion portion 31 can be reduced in size, and the degree of freedom in selecting the light guide member used in the endoscope illumination device 17 is improved.

  In the endoscope illumination device 17, the light emitted from the first excitation light source 25 has a wavelength in the wavelength band of 380 nm to 450 nm, and the light emitted from the second excitation light source 27 is 690 nm to 820 nm. Of the wavelength band.

  In the endoscope illumination device 17, the light emitted from the first excitation light source 25 is light in a blue region of 380 to 450 nm. Therefore, the endoscope illumination device 17 can easily irradiate pseudo white light by configuring the phosphor 33 as a yellow phosphor. Further, the endoscope illumination device 17 uses excitation light having a wavelength band of 690 nm to 820 nm as light emitted from the second excitation light source 27, so that, for example, a fluorescent agent such as ICG known to be harmless to the human body. Excitation light having a wavelength suitable for excitation of the light can be irradiated.

  In addition, the endoscope illumination device 17 is connected to the optical fiber 29 in the insertion portion 31, and enters the light from the light emitting end of the optical fiber 29 (an example of a first optical member). The second prism 49 (second optical) that rotates integrally with the camera 21 rotatably supported at the distal end of the insertion portion 31 and deflects the light incident from the first prism 47 to irradiate the subject. An example of a member). The phosphor 33 is provided at the light emitting end of the second prism 49. Note that, as described above, the first optical member and the second optical member are not limited to the first prism 47 and the second prism 49, respectively, and may be configured by a mirror or the like.

  In the endoscope illumination device 17, the first prism 47 constituting the optical deflector 45 is connected to the light emitting end of the optical fiber 29 disposed at the distal end of the insertion portion 31. The first prism 47 directs the light emitted from the light emitting end of the optical fiber 29 to the axis of the optical fiber 29, for example, in the orthogonal direction. The camera 21 is rotatably supported at the distal end of the insertion portion 31. A second prism 49 that constitutes the optical deflector 45 together with the first prism 47 is integrally fixed to the camera 21. That is, the first prism 47 and the second prism 49 are declination prisms that change the direction of light rays. The light incident surface of the second prism 49 is connected in parallel with and substantially in contact with the light emitting surface of the first prism 47. The second prism 49 is rotatable relative to the first prism 47 integrally with the camera 21 around a rotation center perpendicular to the opposing connection surface. The light exit end of the second prism 49 is directed in the same direction as the imaging direction of the camera 21. That is, in the endoscope illumination device 17, the illumination direction is variable in synchronization with the direction of the camera 21. As a result, the endoscope illumination device 17 can accurately irradiate the imaging portion of the subject with the emitted light in a small space. In this case, the phosphor 33 is a transmission type provided at the light emitting end of the second prism 49. The transmissive phosphor 33 can increase the light transmission efficiency (that is, the illumination efficiency) compared to the reflective type.

  In addition, the endoscope illumination device 17 is connected to a light guide member (for example, an optical fiber 29) in the insertion portion 31 so that light from a light emitting end of the optical fiber 29 is incident on the first optical member ( For example, the first prism 47) and the second optical member that rotates integrally with the camera 21 rotatably supported at the distal end of the insertion portion 31 to deflect the light incident from the first prism 47 and irradiate the subject. (For example, the second prism 49). The phosphor 33 is provided between the first prism 47 and the second prism 49.

  In the endoscope illumination device 17, similarly to the above configuration, the emitted light can be accurately irradiated onto the imaging region of the subject in a space-saving manner in synchronization with the rotation direction of the camera 21. In this case, the phosphor 33 is a transmission type provided between the first prism 47 and the second prism 49. The transmissive phosphor 33 can increase the light transmission efficiency compared to the reflective type. In addition to this, the phosphor 33 provided between the first prism 47 and the second prism 49 is less likely to interfere with other members, and can suppress leakage of excitation light due to cracks or the like.

  In addition, the endoscope illumination device 17 is connected to a light guide member (for example, an optical fiber 29) in the insertion portion 31 so that light from a light emitting end of the optical fiber 29 is incident on the first optical member ( For example, the first prism 47) and the second optical member that rotates integrally with the camera 21 rotatably supported at the distal end of the insertion portion 31 to deflect the light incident from the first prism 47 and irradiate the subject. (For example, the second prism 49) and a reflector 61 that holds the phosphor 33 so as to face the second prism 49 are provided. The phosphor 33 is provided between the second prism 49 and the reflection plate 61.

  In the endoscope illumination device 17, similarly to the above-described configuration, the emitted light can be accurately irradiated onto the imaging region of the subject in synchronization with the rotation direction of the camera 21. In this case, the phosphor 33 is a reflection type provided between the second prism 49 and the reflection plate 61. The reflection type phosphor 33 is provided between the second prism 49 and the reflection plate 61 as in the case of the transmission type. Therefore, the reflection type phosphor 33 is less likely to interfere with other members, and excitation light leakage due to cracks or the like can be suppressed. In addition, the reflective phosphor 33 is advantageous in terms of heat countermeasures compared to the transmissive type.

  In addition, the endoscope system 11 monitors an imaging illumination signal 17, a camera 21 provided at the distal end of the insertion unit 31, and a captured image signal based on an imaging signal of an affected part of a subject captured by the camera 21. 15 and a camera controller 13 that outputs to 15.

  In the endoscope system 11 according to Embodiment 1, the camera 21 and the camera controller 13 are connected by a transmission cable 23. An imaging signal output from the imaging device 57 of the camera 21 is transmitted to the camera controller 13 via the transmission cable 23. The camera controller 13 performs image processing on the transmitted imaging signal, converts the captured image signal after the image processing into a display signal, and outputs the display signal to the monitor 15. The endoscope system 11 includes the endoscope illumination device 17, thereby suppressing a visible light image acquired by visible light and a fluorescent image generated by excitation light while suppressing an increase in the diameter of the insertion portion 31. It can be displayed on the monitor 15.

  Further, in the endoscope system 11, the camera controller 13 includes a visible light image (that is, an RGB image G <b> 1) captured under the illumination environment of the light emitted from the first excitation light source 25, and the second excitation light source 27. The fluorescent image captured in the environment of the illumination of the light irradiated from is displayed on the monitor 15 in contrast.

  In this endoscope system 11, the camera controller 13 executes the simultaneous output mode. In the simultaneous output mode, a visible light image (that is, RGB image G1) and a fluorescence image (that is, IR image G2) are simultaneously output on separate screens. That is, the monitor 15 divides the screen into a plurality of parts (for example, two parts) and displays the visible light image or the fluorescent image side by side on each screen. As a result, a doctor or the like can observe the affected area by comparison on another screen.

  In the endoscope system 11, the camera controller 13 adds the second excitation light source 27 to the visible light image (that is, the RGB image G <b> 1) captured in the illumination environment of the light emitted from the first excitation light source 25. The image of the portion where the fluorescent agent emits fluorescence (that is, the image portion of the affected area TG) is superimposed on the monitor 15 in the fluorescent image (that is, the IR image G2) captured under the illumination environment of the light emitted from indicate.

  In this endoscope system 11, the camera controller 13 executes a superimposition output mode. In the superimposed output mode, a visible light image (that is, RGB image G1) and a fluorescence image (that is, IR image G2) are output as a composite image GZ superimposed on the same screen. As a result, the endoscope system 11 integrates the imaging information of the normal site and the affected area on one screen, and enables simple observation of the affected area that does not require comparison with another image.

  In the endoscope system 11, the camera controller 13 performs control to alternately irradiate (output) the light from the first excitation light source 25 and the light from the second excitation light source 27 in a time division manner. A fluorescence image based on the light from the second excitation light source 27 is acquired at an imaging timing that does not overlap with the irradiation timing by the light from the excitation light source 25.

  In the endoscope system 11, a fluorescence image at the irradiation timing by the light from the second excitation light source 27 is acquired at an imaging timing that does not overlap with the irradiation timing by the light from the first excitation light source 25. That is, the visible light that is reflected when the light of the first excitation light source 25 is applied to the subject does not overlap with the fluorescence generated by exciting the drug fluorescence with the light of the second excitation light source 27. Thereby, the endoscope system 11 can separate the visible light obtained from the subject and the weak fluorescence, and can suppress the deterioration of the image quality of the fluorescence image.

  Therefore, according to the endoscope system 11 according to the first embodiment, it is possible to suppress the increase in diameter of the insertion portion 31 and display a visible light image and a fluorescent image.

  While various embodiments have been described above with reference to the drawings, it goes without saying that the present disclosure is not limited to such examples. It is obvious for those skilled in the art that various modifications, modifications, substitutions, additions, deletions, and equivalents can be conceived within the scope of the claims. Of course, it is understood that it belongs to the technical scope of the present disclosure. In addition, the constituent elements in the various embodiments described above may be arbitrarily combined without departing from the spirit of the invention.

  In the endoscope illumination device 17 according to the first embodiment described above, a multiplexing optical member (for example, multiplexing) that multiplexes (that is, combines) the light in the blue region and the light in the infrared region as the optical multiplexing unit (for example, The configuration using the multiplexing prism 35) has been described. However, the optical multiplexing means is not limited to the example of the optical member for multiplexing described above (see FIG. 13).

  FIG. 13 is a block diagram illustrating a modification of the internal configuration of the endoscope illumination device. In FIG. 13, the same components as those shown in FIG. 2 are denoted by the same reference numerals, description thereof is simplified or omitted, and different contents will be described.

  The endoscope illumination device 17A includes a first excitation light source 25 (an example of a first light source), a second excitation light source 27 (an example of a second light source), optical fibers 29A and 29B, an insertion unit 31, and a fluorescent light. And a body 33 as a main component.

  The optical fibers 29A and 29B are configured by, for example, fiber strands or fiber bundles (that is, fiber bundles). The optical fibers 29A and 29B have base ends arranged on the opposite sides of the first excitation light source 25 and the second excitation light source 27 with the condenser lenses 41A and 41B arranged in the casing of the endoscope illumination device 17A interposed therebetween. Is done. Further, the optical fibers 29A and 29B are bent from the respective base ends toward the branch portion 36 and converged so as to be accommodated in the fiber protection tube 29TB. Further, the optical fibers 29A and 29B extend further from the branch portion 36 along the fiber protection tube 29TB toward the distal end of the endoscope portion 19 so that the respective distal ends can guide light to the phosphor 33. Provided.

  Therefore, the light emitted and output from the first excitation light source 25 is incident on the optical fiber 29A via the condenser lens 41A and guided to the phosphor 33. Similarly, light emitted and output from the second excitation light source 27 is incident on the optical fiber 29B through the condenser lens 41B and guided to the phosphor 33. According to the configuration of this modification, the configuration of the optical multiplexing optical member (for example, the multiplexing prism 35) of the endoscope illumination device 17 according to the first embodiment described above can be made unnecessary, and the endoscope illumination. The configuration of the apparatus can be simplified.

  The present disclosure is useful as an endoscope illumination device and an endoscope system that can suppress an increase in the diameter of an insertion portion and can support imaging of visible light and fluorescence in an endoscope.

DESCRIPTION OF SYMBOLS 11 Endoscope system 13 Camera controller 15 Monitor 17 Endoscopic illumination device 21 Camera 25 1st excitation light source 27 2nd excitation light source 29 Optical fiber 31 Insertion part 33 Phosphor 35 Combined prism 47 First prism 49 Second prism

Claims (14)

A first light source;
A second light source that outputs light having a wavelength including an infrared region for exciting the fluorescent material, which is different from the light emitted from the first light source;
Optical multiplexing means for guiding light emitted from each of the first light source and the second light source and having different wavelength characteristics to the same light guide member;
An insertion portion for inserting the light guide member;
Wavelength conversion is performed on at least a part of the light emitted from each of the first light source and the second light source, provided in an optical path through which lights having different wavelength characteristics are combined and propagated. And an optical element that transmits at least a part of the light emitted from the second light source,
Endoscopic illumination device. The optical element is a phosphor;
The endoscope illumination device according to claim 1. The optical element is disposed at a light incident end or a light exit end of the light guide member,
The first light source emits light in a first wavelength region for causing the optical element to emit light,
The second light source irradiates the light in the second wavelength region including the infrared region for exciting the fluorescent substance,
The optical multiplexing means is a multiplexing means for multiplexing the light in the first wavelength region and the light in the second wavelength region.
The endoscope illumination device according to claim 1 or 2. The first light source and the second light source are configured using a semiconductor laser.
The endoscope illumination device according to claim 1 or 2. The light guide member has a circular cross-sectional shape orthogonal to the direction of the axis, and its outer diameter is 5 mm or less.
The endoscope illumination device according to claim 1 or 2. The light guide member has a cross-sectional area of 80 mm ² or less in a cross-sectional shape orthogonal to the direction of the axis.
The endoscope illumination device according to claim 1 or 2. The light emitted from the first light source has a wavelength in the wavelength band of 380 nm to 450 nm,
The light emitted from the second light source has a wavelength in the wavelength band of 690 nm to 820 nm.
The endoscope illumination device according to claim 1 or 2. A first light source;
A second light source that outputs light having a wavelength different from that of the light emitted from the first light source;
Optical multiplexing means for guiding light emitted from each of the first light source and the second light source and having different wavelength characteristics to the same light guide member;
An insertion portion for inserting the light guide member;
Wavelength conversion is performed on at least a part of the light emitted from each of the first light source and the second light source, provided in an optical path through which lights having different wavelength characteristics are combined and propagated. And an optical element that transmits at least part of the light emitted from the second light source,
A first optical member that is connected to the light guide member and allows light from a light emitting end of the light guide member to enter the insertion portion, and a camera portion that is rotatably supported at the distal end of the insertion portion And a second optical member that deflects and irradiates light incident from the first optical member.
The optical element is provided at a light emitting end of the second optical member ;
Endoscope illumination device. A first light source;
A second light source that outputs light having a wavelength different from that of the light emitted from the first light source;
Optical multiplexing means for guiding light emitted from each of the first light source and the second light source and having different wavelength characteristics to the same light guide member;
An insertion portion for inserting the light guide member;
Wavelength conversion is performed on at least a part of the light emitted from each of the first light source and the second light source, provided in an optical path through which lights having different wavelength characteristics are combined and propagated. And an optical element that transmits at least part of the light emitted from the second light source,
A first optical member that is connected to the light guide member and allows light from a light emitting end of the light guide member to enter the insertion portion, and a camera portion that is rotatably supported at the distal end of the insertion portion And a second optical member that deflects and irradiates light incident from the first optical member.
The optical element is provided between the first optical member and the second optical member .
Endoscope illumination device. A first light source;
A second light source that outputs light having a wavelength different from that of the light emitted from the first light source;
Optical multiplexing means for guiding light emitted from each of the first light source and the second light source and having different wavelength characteristics to the same light guide member;
An insertion portion for inserting the light guide member;
Wavelength conversion is performed on at least a part of the light emitted from each of the first light source and the second light source, provided in an optical path through which lights having different wavelength characteristics are combined and propagated. And an optical element that transmits at least part of the light emitted from the second light source,
A first optical member that is connected to the light guide member and allows light from a light emitting end of the light guide member to enter the insertion portion, and a camera portion that is rotatably supported at the distal end of the insertion portion And a second optical member that deflects and irradiates light incident from the first optical member, and a reflector that holds the optical element facing the second optical member. ,
The optical element is provided between the second optical member and the reflector .
Endoscope illumination device. The endoscope illumination device according to any one of claims 1 to 10,
A camera part provided at the tip of the insertion part;
A camera controller that outputs a captured image signal based on an imaging signal of an affected area of the subject imaged by the camera unit to a monitor;
Endoscope system. The camera controller includes a visible light image captured in an environment of light illumination emitted from the first light source, and a fluorescent image captured in an environment of light illumination emitted from the second light source. Display in contrast to the monitor,
The endoscope system according to claim 11. Among the fluorescent images captured by the camera controller in a light illumination environment irradiated with light emitted from the first light source, and a visible light image captured in the environment illuminated by light emitted from the second light source. An image of a portion where the fluorescent agent emits fluorescence is superimposed and displayed on the monitor,
The endoscope system according to claim 11. The camera controller
Performing control to irradiate the light from the first light source and the light from the second light source in a time-sharing manner;
Obtaining a fluorescence image based on the light from the second light source at an imaging timing that does not overlap with the irradiation timing of the light from the first light source;
The endoscope system according to claim 11.

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