WO2013094569A1 - 内視鏡用照明ユニット及び内視鏡 - Google Patents
内視鏡用照明ユニット及び内視鏡 Download PDFInfo
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- WO2013094569A1 WO2013094569A1 PCT/JP2012/082699 JP2012082699W WO2013094569A1 WO 2013094569 A1 WO2013094569 A1 WO 2013094569A1 JP 2012082699 W JP2012082699 W JP 2012082699W WO 2013094569 A1 WO2013094569 A1 WO 2013094569A1
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- phosphor
- light
- diameter
- endoscope
- protective cover
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/00112—Connection or coupling means
- A61B1/00121—Connectors, fasteners and adapters, e.g. on the endoscope handle
- A61B1/00126—Connectors, fasteners and adapters, e.g. on the endoscope handle optical, e.g. for light supply cables
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/0653—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements with wavelength conversion
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/00064—Constructional details of the endoscope body
- A61B1/00071—Insertion part of the endoscope body
- A61B1/0008—Insertion part of the endoscope body characterised by distal tip features
- A61B1/00096—Optical elements
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/0661—Endoscope light sources
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/0661—Endoscope light sources
- A61B1/0676—Endoscope light sources at distal tip of an endoscope
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
- G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
- G02B23/2407—Optical details
- G02B23/2461—Illumination
- G02B23/2469—Illumination using optical fibres
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/063—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements for monochromatic or narrow-band illumination
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
- A61B1/0661—Endoscope light sources
- A61B1/0684—Endoscope light sources using light emitting diodes [LED]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/30—Devices for illuminating a surgical field, the devices having an interrelation with other surgical devices or with a surgical procedure
- A61B2090/304—Devices for illuminating a surgical field, the devices having an interrelation with other surgical devices or with a surgical procedure using chemi-luminescent materials
Definitions
- the present invention relates to an endoscope illumination unit and an endoscope.
- Endoscopes such as medical endoscopes for observing or treating the inside of a living body are provided with an illumination window and an observation window at the tip of the endoscope insertion portion, and illumination light is emitted from the illumination window.
- the observation image is acquired through the observation window.
- a light source device such as a xenon lamp is guided to and emitted from the illumination window by a light guide member such as an optical fiber bundle.
- a laser light source is used to generate illumination light by exciting and emitting a phosphor disposed at the distal end of an endoscope insertion portion (for example, Patent Documents 1, 2).
- the endoscope apparatus has a strong demand for acquisition of a higher-definition photographed image and photographing at a high frame rate, and high intensity illumination light is desired. Therefore, as in Patent Document 2, a highly reflective reflective film made of a metal film such as silver or aluminum is provided around the phosphor in order to effectively use the excited light as illumination light.
- the endoscope insertion portion be configured with a diameter as small as possible in order to reduce the burden on the patient or the like.
- the outer diameter of the illumination unit is increased, and the endoscope insertion portion is increased in diameter accordingly.
- the present invention has been made in view of the above problems, and provides an endoscope illumination unit and an endoscope that can obtain high-intensity irradiation light while suppressing an increase in diameter of an endoscope insertion portion. With the goal.
- the present invention is an illumination unit that is attached to the distal end of an insertion portion of an endoscope.
- the illumination unit guides and emits laser light from a light source to the distal end, and is excited by the laser light emitted from the optical fiber to fluoresce.
- a phosphor that emits light a phosphor holding portion that holds the phosphor at one end, a ferrule that communicates with the phosphor holding portion and has an insertion hole through which an optical fiber is inserted at the other end.
- the emission light efficiency (B2 / B1) is preferably 90% or more when the emission amount within the range of the emission diameter D1 is B1 and the emission amount within the range of the effective diameter D2 is B2.
- an endoscope according to the present invention includes the illumination unit.
- the emission diameter is D1
- the effective diameter of the protective cover is D2
- the thickness is t1
- the emission diameter D1 is 0.7 mm ⁇ D1 ⁇ .
- FIG. 1 It is sectional drawing which shows the illumination unit of this invention. It is a disassembled perspective view of an illumination unit. It is sectional drawing which shows the shape and dimension of a protective cover, a fluorescent substance, a metal reflective film, and a ferrule. It is a graph which shows light distribution of a fluorescent substance. It is explanatory drawing which shows the example of sensor arrangement
- 6 is a graph showing the relationship between the effective diameter D2 of the protective cover and the emission light efficiency, with the thickness t1 of the protective cover being 0.59 mm, and changing the emission diameter D1 of the phosphor in three stages of S4, S5, and S6.
- the illumination unit 10 of the present invention includes a protective cover 11, a sleeve 12, a phosphor 13, a metal reflecting film 14, a ferrule 15, and an optical fiber 16 in order from the tip.
- a first sealing portion 17 is formed between the protective cover 11 and the upper end (one end) of the sleeve 12, and a second sealing portion 18 is formed between the lower end (the other end) of the sleeve 12 and the ferrule 15. .
- the sleeve 12 is formed in a cylindrical shape having an inner peripheral surface 12a, and a cover receiving portion 21 for attaching the protective cover 11 is formed at one end.
- the sleeve 12 is made of stainless steel, nickel, copper, a copper-tungsten alloy, a copper-molybdenum-based composite material, a hard material such as phosphor bronze, or carbon.
- the cover receiving portion 21 is formed by cutting out the inner peripheral surface 12a of the sleeve 12 in a step shape, and includes a step portion surface 21a and an inner peripheral surface 21b.
- the protective cover 11 is configured in a disc shape using, for example, sapphire glass or quartz glass.
- a coat layer for transmitting light in the vicinity of 445 nm, for example is provided.
- a part of the protective cover 11 protrudes from the cover receiving portion 21.
- a sealing agent is deposited between the protruding outer peripheral surface 11 a of the protective cover 11 and the tip end surface 12 b of the sleeve 12 to form the first sealing portion 17.
- the sealant for example, an epoxy adhesive that does not volatilize siloxy acid is preferably used.
- the ferrule 15 is fitted into the inner peripheral surface 12 a of the sleeve 12 and is disposed in the sleeve 12.
- a phosphor holder 22 is formed at the tip of the ferrule 15.
- the phosphor holding part 22 is configured by a hole for housing the phosphor 13 and has a bottom surface 22a, an inner peripheral surface 22b, and an expanded inner peripheral surface 22c.
- the metal reflecting film 14 is formed on the bottom surface 22a and the inner peripheral surfaces 22b and 22c of the phosphor holder 22.
- the metal reflective film 14 is formed by plating, vapor deposition, sputtering, or the like, and silver or aluminum is used. In particular, silver is preferably used because of its high reflectance.
- an organic sulfidation preventing layer may be formed on the surface of silver, or bismuth may be added to silver to improve reflectivity and corrosion resistance. Further, if a sufficient thickness can be secured, an alumina reflective film may be used instead of the metal reflective film 14.
- the metal reflection film 14 is formed on each surface 22a, 22b, 22c of the phosphor holding part 22 in this way, the light emitted from the phosphor 13 is repeatedly reflected by the metal reflection film 14 to make high use of light. It can be injected to the protective cover 11 side with efficiency.
- reference numerals 14a, 14b, and 14c are attached to the reflective films on the respective surfaces 22a to 22c so as to correspond to the bottom surface 22a, the inner peripheral surface 22b, and the spread inner peripheral surface 22c.
- the phosphor 13 is formed in a substantially cylindrical shape having a conical surface 13a at the tip.
- the phosphor 13 constitutes a plurality of kinds of phosphors (for example, YAG phosphor or phosphor such as BAM (BaMgAl 10 O 17 )) that absorbs a part of blue laser light and emits green to yellow light. It is configured to include a fluorescent material and a fixing / solidifying resin serving as a filler. As a result, green to yellow excitation light using blue laser light as excitation light and blue laser light transmitted without being absorbed by the phosphor 13 are combined to form white (pseudo-white) illumination light.
- YAG phosphor or phosphor such as BAM (BaMgAl 10 O 17 )
- a semiconductor light emitting device is used as an excitation light source, high intensity white light can be obtained with high luminous efficiency, the intensity of white light can be easily adjusted, and the color temperature and chromaticity of white light can be changed. It can be kept small.
- an insertion hole 23 through which the optical fiber 16 is inserted is formed along the center line of the ferrule 15.
- the insertion hole 23 opens in the bottom surface 22 a of the phosphor holding unit 22.
- the optical fiber 16 is inserted through the opening so that the tip of the optical fiber 16 is exposed.
- the other end of the optical fiber 16 is connected to a light source device 52 (see FIG. 14), and laser light from the light source device 52 is irradiated toward the phosphor 13 in the phosphor holding unit 22.
- the ferrule 15 is also made of the same metal or resin as the sleeve 12. By forming the sleeve 12 and the ferrule 15 with a high thermal conductivity material such as the above metal, heat generated in the vicinity of the phosphor 13 can be quickly diffused, and local heating is prevented.
- the inner peripheral surface 12 a of the lower end portion of the sleeve 12 is filled with a sealing agent, and the second sealing portion 18 is configured.
- the second sealing portion 18 is filled in a gap between the sleeve 12 and the ferrule 15 and the optical fiber 16 to seal the ferrule 15 in the sleeve 12. Thereby, the phosphor 13 and the metal reflection film 14 held by the ferrule 15 are blocked from the outside.
- the protective tube 25 is put on the rear end of the sleeve 12.
- the protective tube 25 protects the built-in optical fiber 16.
- the optical fiber 16 includes a single-mode or multi-mode fiber main body 16a and a protective layer 16b serving as an outer skin.
- FIG. 3 shows the positional relationship between the protective cover 11 and the phosphor 13 in a state where the ferrule 15 is placed in the sleeve 12 (see FIG. 1).
- FIG. 4 shows the light distribution at a position 100 mm away from the phosphor 13 having a light emitting surface diameter (emission diameter D1) of 0.8 mm, and shows the results measured in the state shown in FIG. ing.
- the emission diameter D1 of the phosphor 13 refers to the maximum diameter of the metal reflection film 14 when the metal reflection film 14 is provided around.
- the phosphor light distribution is measured by using an illuminance measuring device 28 having a sensor frame 27 with respect to the protective cover 11 and the phosphor 13 which are light sources to be measured.
- the sensor frame 27 is configured by arranging the light receivers 26 at intervals of, for example, 5 ° in the circumferential direction so that the distance L1 is 100 mm on the circumference of a circle having the measurement target light source as the center point C1. Signals from the respective light receivers 26 of the sensor frame 27 are converted into illuminance by the illuminance measuring device 28 and displayed on the display as a phosphor light distribution as shown in FIG.
- the illuminance 4 is obtained by plotting the light distribution angle (°) on the horizontal axis and the illuminance on the vertical axis.
- the illuminance is determined based on the illuminance at the light distribution angle of 0 ° as the maximum illuminance “1”.
- the sensor frame 27 and the illuminance measuring device 28 are used to calculate the illuminance (illuminance by the phosphor 13) B1 on the light emitting surface M1 in FIG. 3 and the illuminance (illuminance when transmitted through the protective cover 11) B2 on the light emitting surface M2 in FIG. To determine B2 / B1 as the emission light efficiency.
- the emission light efficiency (B2 / B1) is obtained for each thickness when the thickness t1 of the protective cover 11 is between 0.4 and 0.59 mm.
- FIG. 7 shows the relationship between the emission light efficiency (B2 / B1) and the thickness t1 of the protective cover 11, where the effective diameter D2 of the protective cover 11 is 1.3 mm, the emission diameter D1 of the phosphor 13 is 0.9 mm, and. It is the graph calculated
- the effective diameter D2 means the diameter of the circle
- S1 shows a characteristic curve when the injection diameter D1 is 0.9 mm
- S2 shows a characteristic curve when the injection diameter D1 is 0.8 mm
- S3 shows a characteristic curve when the injection diameter D1 is 0.7 mm.
- FIG. 8 shows the relationship between the emission light efficiency (B2 / B1) and the effective diameter D2 of the protective cover 11.
- the thickness t1 of the protective cover 11 is 0.59 mm
- the emission diameter D1 is 0.9 mm, 0.8 mm,. It is the graph calculated
- S4 shows a characteristic curve when the injection diameter D1 is 0.9 mm
- S5 shows a characteristic curve when the injection diameter D1 is 0.8 mm
- S6 shows a characteristic curve when the injection diameter D1 is 0.7 mm.
- the effective diameter D2 of the protective cover is within a range of 1.3 mm ⁇ D2 ⁇ 1.5 mm, and the injection is 90% or more at any thickness t1. It can be seen that light efficiency is obtained. Further, when the thickness t1 of the protective cover 11 is increased, the emission light efficiency is lowered as is apparent from FIG. 7, and therefore, when the thickness t1 exceeds 0.59 mm, the emission diameter D1 of the phosphor is determined from the relationship of FIG. In the case of 0.9 mm, the emission light efficiency is lowered to near 0.9, which is not preferable.
- the thickness t1 of the protective cover 11 is less than 0.59 mm, since the protective cover 11 is in a direction of thinning, the emission light efficiency is higher, so the thickness t1 is within the range of 0.59 mm or more. There is no particular problem even if the range of the protective cover effective diameter D2 is obtained.
- LightTools manufactured by Synopsys is used as a simulation application, and measurement data is reproduced using, for example, a cos 1.37 power scattering surface as a light source definition for simulation, for example. You may go.
- the protective cover 11 is provided with a coating layer to increase the emission light efficiency.
- the effective diameter D2 of the protective cover 11 is not limited to an upper limit of 1.5 mm only from the viewpoint of improving the emission light efficiency, but the effective diameter D2 of the protective cover 11 should be a value exceeding 1.5 mm. This is not preferable because the diameter of the illumination unit 10 is increased, and accordingly, the diameter of the endoscope insertion portion is also increased. On the other hand, if it is less than 1.3 mm, as can be seen from FIG. 8, the emission light efficiency becomes 0.9 or less, particularly when the emission diameter D1 is 0.9 mm, or the effective diameter D2 of the phosphor 13. As the diameter decreases, the amount of light emission also decreases, which is not preferable.
- the amount of illumination light is increased by the increase in the reflected light by the spread reflection film 14c.
- the phosphor 13 may be formed on a conical surface 13a in which the outer peripheral surface portion of the phosphor 13 facing the spread-spreading reflective film 14c is cut into a cone in accordance with the spread-spreading reflective film 14c.
- the light emitting area that can be used as illumination light can be increased, and the overall illumination light quantity may increase.
- the spread angle ⁇ 1 of the spread reflection film 14c with respect to the holding hole inner peripheral surface 14b is preferably 15 ° or more and 60 ° or less.
- light emitted from the conical surface 13a or the outer peripheral surface of the phosphor 13 is also used as illumination light. It can be used effectively and efficiency is improved.
- a part of the outer peripheral surface of the phosphor 13 is formed on the conical surface 13a in accordance with the spread reflection film 14c.
- the metal reflecting film 32 may be used only for the bottom surface 31a and the outer peripheral surface 31b of the phosphor holder 31 without forming the spread-expanded reflecting film 14c on the ferrule 33.
- a columnar phosphor 30 as shown in FIG. 9 may be used for the phosphor holder 22 and the metal reflection film 14 as shown in FIG.
- a phosphor 13 having a conical surface 13a at the tip as shown in FIG. 1 may be used for the ferrule 33 having the phosphor holding portion 31 shown in FIG.
- the same member is denoted by the same reference numeral, and redundant description is omitted.
- the first sealing portion 17 is composed of a sealing agent that is formed on a part of the outer peripheral surface 11 a of the protective cover 11 and a part of the front end surface 12 b of the sleeve 12.
- a sealing agent receiving step portion 35 comprising a step portion surface 35a and an inner peripheral surface 35b is provided on the distal end surface of the sleeve 12, and this sealing agent receiving step portion 35 is provided.
- the first sealing portion 36 may be configured by depositing a sealing agent. In this case, the front end corner portion of the protective cover 11 does not protrude outside and is protected by the front end portion of the sleeve 37.
- the second sealing portion 18 collectively seals between the sleeve 12 and the ferrule 15 and between the ferrule 15 and the optical fiber 16.
- sealing agents are individually sealed between the ferrule 15 and the optical fiber 16 and between the outer peripheral surface of the ferrule 15 and the inner peripheral surface of the sleeve 12.
- the second sealing portion 18 may be configured.
- the illumination unit 10 of the present invention is used by being incorporated in the distal end portion 56a of the insertion portion of the electronic endoscope 50.
- the electronic endoscope 50 is connected to a processor device 51 and a light source device 52, and the electronic endoscope system 53 is configured by the electronic endoscope 50, the processor device 51, and the light source device 52.
- the electronic endoscope 50 is connected to a flexible insertion portion 56 that is inserted into a body cavity of a patient, an operation portion 57 that is connected to a proximal end portion of the insertion portion 56, a processor device 51, and a light source device 52.
- Connector 58, and a universal cord 59 connecting the operation portion 57 and the connector 58.
- the insertion portion 56 includes a distal end portion 56a, a bending portion 56b, and a flexible tube portion 56c in order from the distal end.
- An imaging unit and the illumination unit 10 of the present invention are built in the distal end portion 56a.
- the bending portion 56b is configured to be freely bent by a wire operation.
- the flexible tube portion 56 c has flexibility and connects the bending portion 56 b and the operation portion 57.
- the operation portion 57 is provided with operation members such as an angle knob 61 for bending the bending portion 56b vertically and horizontally and an air / water supply button 62 for ejecting air and water from the tip portion 56a.
- the operation unit 57 is provided with a forceps port 63 for inserting a treatment tool such as an electric knife into a forceps channel (not shown).
- the processor device 51 is electrically connected to the light source device 52 and comprehensively controls the operation of the electronic endoscope system 53.
- the processor device 51 supplies power to the electronic endoscope 50 via the universal cord 59 and a transmission cable inserted into the insertion portion 56 and drives the imaging unit 64. Further, the processor device 51 acquires an imaging signal output from the imaging unit 64 via a transmission cable, and performs various image processing to generate image data.
- the image data generated by the processor device 51 is displayed on the monitor 65 as an observation image.
- the distal end portion 56a includes a distal end rigid portion 66 and a distal end protective cap 67 attached to the distal end side of the distal end rigid portion 66.
- the distal end hard portion 66 is made of, for example, stainless steel, and a plurality of through holes are formed along the longitudinal direction.
- Various components such as two illumination units 10, an imaging unit 64, a forceps channel, an air / water supply channel (not shown), and the like are attached to each through hole of the distal end rigid portion 66.
- the rear end of the distal end rigid portion 66 is coupled to the distal bending piece 68 constituting the bending portion 56b.
- the outer periphery of the distal end rigid portion 66 is covered with an outer tube 69.
- the tip protection cap 67 is made of rubber or resin elastomer, and a through hole is formed at a position corresponding to various parts held by the tip rigid portion 66. As shown in FIG. 13, the tip protection cap 67 exposes an observation window 70, two (one pair) illumination units 10, a forceps outlet 71, an air / water supply nozzle 72 and the like from each through hole.
- the pair of illumination units 10 are arranged at symmetrical positions with the observation window 70 in between.
- an imaging unit 64 and two illumination units 10 are provided at the distal end portion 56a, and an AFE (analog signal processing circuit) 73 and an imaging control unit 74 are provided in the operation unit 57. Is provided.
- the imaging unit 64 is disposed in the back of the observation window 70, and includes an imaging optical system 76 including a lens group and a prism, and a CCD 77 on which an image in the body cavity is formed on the imaging surface by the imaging optical system 76.
- the CCD 77 photoelectrically converts an image in the subject formed on the imaging surface to accumulate signal charges, and outputs the accumulated signal charges as an imaging signal.
- the output imaging signal is sent to the AFE 73.
- the AFE 73 includes a correlated double sampling (CDS) circuit, an automatic gain adjustment (AGC) circuit, an A / D converter, and the like (all not shown).
- the CDS performs correlated double sampling processing on the imaging signal output from the CCD 77 to remove noise generated by driving the CCD 77.
- the AGC amplifies the imaging signal from which noise has been removed by CDS.
- the imaging control unit 74 is connected to the controller 85 in the processor device 51 when the electronic endoscope 50 and the processor device 51 are connected, and sends a drive signal to the CCD 77 when an instruction is issued from the controller 85. .
- the CCD 77 outputs an imaging signal to the AFE 73 at a predetermined frame rate based on the drive signal from the imaging control unit 74.
- the optical fiber 16 of the illumination unit 10 guides the blue laser light supplied from the light source device 52 and emits it to the phosphor 13 provided on the emission end side.
- the phosphor 13 absorbs part of the blue laser light emitted from the optical fiber 16 and emits light by excitation from green to yellow. For this reason, in the illumination unit 10, the blue light transmitted while diffusing through the phosphor 13 and the green to yellow fluorescence excited and emitted from the phosphor 13 are combined to form white (pseudo white) illumination light. Is done.
- the illumination light irradiation range is about the same as or larger than the photographing range of the electronic endoscope 50, and the illumination light is irradiated almost uniformly on the entire surface of the observation image.
- the processor device 51 includes a digital signal processing circuit (DSP) 81, a digital image processing circuit (DIP) 82, a display control circuit 83, a VRAM 84, a controller 85, an operation unit 86, and the like.
- DSP digital signal processing circuit
- DIP digital image processing circuit
- VRAM VRAM
- controller 85 an operation unit 86, and the like.
- the controller 85 controls the overall operation of the processor device 51 in an integrated manner.
- the DSP 81 performs various signal processing such as color separation, color interpolation, gain correction, white balance adjustment, and gamma correction on the imaging signal output from the AFE 73 of the electronic endoscope 50 to generate image data.
- the image data generated by the DSP 81 is input to the working memory of the DIP 82. Further, the DSP 81 generates ALC control data necessary for automatic control (ALC control) of the illumination light amount, such as an average luminance value obtained by averaging the luminance of each pixel of the generated image data, and inputs the generated data to the controller 85.
- ALC control automatic control
- the DIP 82 performs various image processing such as electronic scaling, color enhancement processing, and edge enhancement processing on the image data generated by the DSP 81.
- Image data that has been subjected to various image processing by the DIP 82 is temporarily stored in the VRAM 84 as an observation image and then input to the display control circuit 83.
- the display control circuit 83 selects and acquires an observation image from the VRAM 84 and displays it on the monitor 65.
- the operation unit 86 includes a known input device such as an operation panel, a mouse, and a keyboard provided in the casing of the processor device 51.
- the controller 85 operates each part of the electronic endoscope system 53 according to operation signals from the operation part 86 and the operation part 57 of the electronic endoscope 50.
- the light source device 52 includes a laser diode (LD) 91 as a laser light source and a light source control unit 92.
- the LD 91 is a light source that emits blue laser light having a central wavelength of 445 nm, and is guided to the optical fiber 93 through a condenser lens (not shown).
- the optical fiber 93 is connected to the two optical fibers 95a and 95b via the branch coupler 94.
- the optical fibers 95 a and 95 b are connected to the optical fiber 16 of the electronic endoscope 50 through the connector 58. For this reason, the blue laser light from the LD 91 is incident on the phosphor 13 constituting the illumination unit 10. Then, when the blue laser light is incident, the green to yellow fluorescence excited by the phosphor 13 and the blue laser light are combined and irradiated to the observation site as white illumination light.
- the light source control unit 92 adjusts the timing of turning on / off the LD 91 according to the adjustment signal and the synchronization signal input from the controller 85 of the processor device 51. Further, the light source control unit 92 communicates with the controller 85 and adjusts the amount of illumination light applied to the observation site by adjusting the light emission amount of the LD 91.
- the illumination light amount control by the light source control unit 92 is ALC (Auto Light Control) control that automatically adjusts the illumination light amount according to the brightness of the taken observation image, and the ALC control data generated by the DSP 81. Based on.
- the illumination unit 10 of the present invention it is possible to illuminate the observation site with high-intensity illumination light, and accordingly, the imaging unit can acquire a high-definition photographed image or at a high frame rate. Can be taken.
- an electronic endoscope that observes an image obtained by imaging the state of an observation site using an image sensor has been described as an example.
- the present invention is not limited to this, and an optical image guide is used.
- the present invention can also be applied to an endoscope that observes using the above.
- an endoscope provided with two illumination optical system units is described as an example.
- the present invention is not limited to this, and an endoscope provided with one illumination optical system unit.
- the present invention can also be applied to an endoscope provided with three or more illumination optical system units.
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- Heart & Thoracic Surgery (AREA)
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Abstract
Description
11 保護カバー
12 スリーブ
13 蛍光体
14 金属反射膜
15 フェルール
16 光ファイバ
17 第1係止部
18 第2係止部
21 カバー受け部
22 蛍光体保持部
50 電子内視鏡
51 プロセッサ装置
52 光源装置
53 電子内視鏡システム
56 挿入部
56a 先端部
Claims (4)
- 内視鏡の挿入部先端部に取り付けられる照明ユニットであって、
光源からのレーザ光を先端部まで導いて出射する光ファイバと、
前記光ファイバから出射されるレーザ光により励起して蛍光を発する蛍光体と、
前記蛍光体を保持する蛍光体保持部を一端に有し、前記蛍光体保持部に連通し、前記光ファイバが挿通される挿通孔を他端に有するフェルールと、
筒状に構成され、前記筒内に前記フェルールを保持するスリーブと、
前記スリーブ内の前記フェルールに保持された前記蛍光体を覆うように、前記スリーブの一端に取り付けられ、前記蛍光体からの光を透過する保護カバーと、
前記保護カバーと前記スリーブとを封止する第1封止部と、
前記スリーブと前記フェルールの他端側を封止する第2封止部とを有し、
前記蛍光体を略円柱体状に構成し、その射出径をD1、前記保護カバーの厚みをt1、前記保護カバーの有効径をD2としたときに、0.7mm≦D1≦0.9mm、かつ0.4mm≦t1≦0.59mm、かつ1.3≦D2≦1.5であることを特徴とする内視鏡用照明ユニット。 - 前記射出径D1の範囲内における発光量をB1とし、前記有効径D2の範囲内における発光量をB2としたときに、射出光効率(B2/B1×100)が90%以上である請求項1記載の内視鏡用照明ユニット。
- 前記フェルールは、前記蛍光体保持部の内周面に光反射膜を有し、
前記蛍光体保持部は、前記蛍光体の外周面の前記他端側を保持する保持孔と、この保持孔の内壁面に連結し、前記蛍光体の外周面の前記一端側に対し次第に開拡する開拡反射膜とを有し、前記蛍光体の射出径D1は前記開拡反射膜の最大開口径である請求項1または2記載の内視鏡用照明ユニット。 - 請求項1から3いずれか1項記載の内視鏡用照明ユニットを有することを特徴とする内視鏡。
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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JP2013550272A JP5649747B2 (ja) | 2011-12-19 | 2012-12-17 | 内視鏡用照明ユニット及び内視鏡 |
EP12858769.8A EP2796082B1 (en) | 2011-12-19 | 2012-12-17 | Illuminating unit for endoscope, and endoscope |
CN201280060683.9A CN103987307B (zh) | 2011-12-19 | 2012-12-17 | 内窥镜用照明单元及内窥镜 |
US14/307,689 US20140296638A1 (en) | 2011-12-19 | 2014-06-18 | Illumination unit for endoscope and endoscope |
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JP2011-277321 | 2011-12-19 | ||
JP2011277321 | 2011-12-19 |
Related Child Applications (1)
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US14/307,689 Continuation US20140296638A1 (en) | 2011-12-19 | 2014-06-18 | Illumination unit for endoscope and endoscope |
Publications (1)
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WO2013094569A1 true WO2013094569A1 (ja) | 2013-06-27 |
Family
ID=48668459
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PCT/JP2012/082699 WO2013094569A1 (ja) | 2011-12-19 | 2012-12-17 | 内視鏡用照明ユニット及び内視鏡 |
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US (1) | US20140296638A1 (ja) |
EP (1) | EP2796082B1 (ja) |
JP (1) | JP5649747B2 (ja) |
CN (1) | CN103987307B (ja) |
WO (1) | WO2013094569A1 (ja) |
Cited By (5)
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CN106455937A (zh) * | 2014-04-29 | 2017-02-22 | 波士顿科学医学有限公司 | 无腔照明系统 |
US20180003945A1 (en) * | 2015-03-25 | 2018-01-04 | Olympus Corporation | Method for measuring scanning pattern of optical scanning apparatus, apparatus for measuring scanning pattern, and method for calibrating image |
US10362931B2 (en) | 2017-05-02 | 2019-07-30 | Panasonic Intellectual Property Management Co., Ltd. | Optical device |
WO2020202883A1 (ja) * | 2019-03-29 | 2020-10-08 | 富士フイルム株式会社 | 内視鏡、内視鏡装置 |
JP7488619B1 (ja) | 2023-10-26 | 2024-05-22 | 株式会社タナカ技研 | カメラヘッド及び撮像システム |
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EP2875772B1 (en) * | 2012-07-19 | 2016-11-30 | Olympus Corporation | Distal end rigid section of insertion portion of endoscope and endoscope |
CN110461203B (zh) * | 2017-03-24 | 2021-12-21 | 奥林巴斯株式会社 | 内窥镜系统 |
KR20200040228A (ko) * | 2017-08-09 | 2020-04-17 | 알콘 인코포레이티드 | 자체 조명식 미세 수술 캐뉼라 장치 |
TWI630345B (zh) | 2017-12-26 | 2018-07-21 | 財團法人工業技術研究院 | 照明裝置 |
JP7091453B2 (ja) * | 2018-06-11 | 2022-06-27 | オリンパス株式会社 | 内視鏡用光接続モジュール、内視鏡、および、内視鏡システム |
EP3903659B1 (en) * | 2020-04-29 | 2023-12-06 | BHS Technologies GmbH | Sterile cover for a medical imaging device and sterile medical imaging system |
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2012
- 2012-12-17 EP EP12858769.8A patent/EP2796082B1/en not_active Not-in-force
- 2012-12-17 JP JP2013550272A patent/JP5649747B2/ja not_active Expired - Fee Related
- 2012-12-17 CN CN201280060683.9A patent/CN103987307B/zh active Active
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CN106455937A (zh) * | 2014-04-29 | 2017-02-22 | 波士顿科学医学有限公司 | 无腔照明系统 |
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WO2020202883A1 (ja) * | 2019-03-29 | 2020-10-08 | 富士フイルム株式会社 | 内視鏡、内視鏡装置 |
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JP7488619B1 (ja) | 2023-10-26 | 2024-05-22 | 株式会社タナカ技研 | カメラヘッド及び撮像システム |
Also Published As
Publication number | Publication date |
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EP2796082B1 (en) | 2016-10-19 |
US20140296638A1 (en) | 2014-10-02 |
CN103987307A (zh) | 2014-08-13 |
EP2796082A1 (en) | 2014-10-29 |
JPWO2013094569A1 (ja) | 2015-04-27 |
CN103987307B (zh) | 2015-08-05 |
EP2796082A4 (en) | 2015-08-26 |
JP5649747B2 (ja) | 2015-01-07 |
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