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Patent US7102142 - Method of apparatus for generating fluorescence diagnostic information - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign in<nobr>Advanced Patent Search</nobr>PatentsFirst fluorescence diagnostic information reflecting a first characteristic value obtained on the basis of first fluorescence information on fluorescence emitted from an object part exposed to first stimulating light is output. Second fluorescence diagnostic information reflecting a second characteristic...http://www.google.com/patents/US7102142?utm_source=gb-gplus-sharePatent US7102142 - Method of apparatus for generating fluorescence diagnostic informationAdvanced Patent SearchPublication numberUS7102142 B2Publication typeGrantApplication numberUS 10/445,061Publication dateSep 5, 2006Filing dateMay 27, 2003Priority dateMay 27, 2002Fee statusPaidAlso published asUS20030218137Publication number10445061, 445061, US 7102142 B2, US 7102142B2, US-B2-7102142, US7102142 B2, US7102142B2InventorsTomonari SendaiOriginal AssigneeFuji Photo Film Co., Ltd.Export CitationBiBTeX, EndNote, RefManPatent Citations (5), Referenced by (5), Classifications (10), Legal Events (4) External Links: USPTO, USPTO Assignment, EspacenetMethod of apparatus for generating fluorescence diagnostic informationUS 7102142 B2Abstract First fluorescence diagnostic information reflecting a first characteristic value obtained on the basis of first fluorescence information on fluorescence emitted from an object part exposed to first stimulating light is output. Second fluorescence diagnostic information reflecting a second characteristic value obtained on the basis of second fluorescence information on fluorescence emitted from an object part exposed to second stimulating light is output. The wavelength of the first stimulating light is such that when the first stimulating light is projected onto clean object parts different in properties, different first characteristic values are obtained from the different object parts, and the wavelength of the second stimulating light is such that when the second stimulating light is projected onto a clean object part and an unclean object part, different second characteristic values are obtained from the clean object part and the unclean object part.
There has been proposed a fluorescence diagnostic information generating apparatus which projects stimulating light of a predetermined wavelength onto an object part such as an organic body and outputs fluorescence diagnostic information such as a fluorescence diagnostic image representing properties of tissue of the object part on the basis of fluorescence emitted from the object part. Such fluorescence diagnostic information generating apparatuses can be divided into those which output fluorescence diagnostic information on the basis of fluorescence emitted from the object part which has been caused to absorb a fluorescence agent and those which output fluorescence diagnostic information on the basis of autofluorescence emitted from the object part itself without use of a fluorescence agent. In this specification, the fluorescence emitted from the object part which has been caused to absorb a fluorescence agent will be sometimes referred to as �the agent fluorescence� and the fluorescence diagnostic information generating apparatus of the former type will be sometimes referred to as �the agent fluorescence diagnostic information generating apparatus�, hereinbelow. Whereas, the fluorescence diagnostic information generating apparatus of the latter type will be sometimes referred to as �the autofluorescence diagnostic information generating apparatus�, hereinbelow. The fluorescence diagnostic information generating apparatus is generally incorporated in an endoscope which is inserted into a body cavity, a colposcope, a surgical microscope or the like.
The object tissue is sometimes stained with disturbance factors such as blood, mucus, digestive fluid, saliva, foam, residue and the like. When an organic tissue stained with such a disturbance factor (will be referred to as �unclean tissue�, hereinbelow) is exposed to the stimulating light, the disturbance factor also emits fluorescence. Fluorescence emitted from an unclean tissue is sometimes confusing with fluorescence emitted from a diseased tissue in the normalized intensity of fluorescence and/or the yield of fluorescence.
SUMMARY OF THE INVENTION In view of the foregoing observations and description, the primary object of the present invention is to provide a method of and apparatus for generating fluorescence diagnostic information which can suppress mistaking an unclean tissue for a clean diseased tissue, thereby improving the tissue-property distinguishing accuracy.
In the method and apparatus described above, the expression �characteristic values are different� need not be limited to meaning the case where the characteristic values are entirely different from each other but may include a case where the characteristic values partly overlap each other so long as they can be substantially separated from each other. For example, the case where distributions of characteristic values obtained from a plurality of clean object parts and distributions of those obtained from a plurality of unclean parts can be substantially separated from each other may be included in cases where characteristic values are different.
As the characteristic value, for instance, the intensity of fluorescence, the shape of spectrum of fluorescence, a normalized intensity of fluorescence reflecting the shape of spectrum of fluorescence or the yield of fluorescence can be employed. The �normalized intensity of fluorescence� is a value which reflects the shape of spectrum of fluorescence, e.g., a proportion of intensities of fluorescence obtained from the object part in different wavelength bands. For example, the �normalized intensity of fluorescence� may be obtained by dividing an intensity of fluorescence in a narrow wavelength band (e.g., 430 nm to 530 nm) by an intensity of fluorescence in a broad wavelength band (e.g., the entire wavelength band or an wavelength band from 430 nm to 730 nm). The �normalized intensity of fluorescence� may be obtained on the basis of a proportion of intensities of fluorescence obtained from the object part in a pair of narrow wavelength bands (e.g., a narrow wavelength band near 480 nm and a narrow wavelength band near 630 nm).
The �yield of fluorescence� means a ratio of the intensity of the stimulating light which the object part receives to the intensity of fluorescence emitted from the object part. The �yield of fluorescence� as used here need not be strictly a ratio of the intensity of the stimulating light which the object part receives to the intensity of fluorescence emitted from the object part so long as it reflects the �yield of fluorescence�. For example, the �yield of fluorescence� may be obtained as a ratio of the intensity of a reference light (as substitution of the intensity of the stimulating light which the object part receives) and the intensity of fluorescence emitted from the object part. The reference light maybe near-infrared light which is relatively uniform in reflecting properties independent of the kind of the tissue. Normal illumination light may be employed as the reference light though the accuracy slightly deteriorates. In the case of, for instance, an endoscope, the intensity of fluorescence may be employed as the yield of fluorescence if fluctuation in the distance between the end face of the endoscope and the object part can be held small.
The first stimulating light projecting means may be provided with a Ga�N semiconductor laser as a source of the first stimulating light. The second stimulating light projecting means may be provided with a Ga�N semiconductor laser as a source of the second stimulating light.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a view showing the shapes of spectra of fluorescences emitted from a clean normal tissue, a clean diseased tissue and an unclean tissue upon exposure to a stimulating light of 360 nm,
DESCRIPTION OF THE PREFERRED EMBODIMENTS A fluorescence endoscope in accordance with a first embodiment of the present invention will be described with reference to FIGS. 3 to 5, hereinbelow.
In the fluorescence diagnosis mode, fluorescence image data in a broad wavelength band of 430 nm to 700 nm is obtained on the basis of fluorescence emitted from the object part 1 upon exposure to the stimulating light Le1 (This fluorescence image data will be referred to as �the broad-band fluorescence image data (Le1)�, hereinbelow), IR reflection image data is obtained on the basis of reflected reference light Ls (near-infrared light) reflected by the object part 1 when the reference light Ls is projected onto the object part 1, a value reflecting the yield of fluorescence (will be referred to simply as �the yield of fluorescence (Le1)�, hereinbelow) is obtained pixel by pixel by dividing the value of each pixel of the broad-band fluorescence image data (Le1) by the value of the corresponding pixel of the IR reflection image data, color information for each pixel is generated on the basis of the yield of fluorescence (Le1) for the pixel, brightness information for each pixel is generated on the basis of the value of the corresponding pixel of the IR reflection image data, and a fluorescence diagnostic image is displayed on the monitor 70 on the basis of combination of the color information and the brightness information. In the disturbance judgment mode, fluorescence image data in a narrow wavelength band of 530 nm to 570 nm is obtained on the basis of fluorescence emitted from the object part 1 upon exposure to the stimulating light Le2 (This fluorescence image data will be referred to as �the narrow-band fluorescence image data (Le2)�, hereinbelow), fluorescence image data in a broad wavelength band of 530 nm to 800 nm is obtained on the basis of fluorescence emitted from the object part 1 upon exposure to the stimulating light Le2 (This fluorescence image data will be referred to as �the broad-band fluorescence image data (Le2)�, hereinbelow), IR reflection image data is obtained on the basis of reflected reference light Ls (near-infrared light) reflected by the object part 1 when the reference light Ls is projected onto the object part 1, a value reflecting the normalized intensity of fluorescence (will be referred to simply as �the normalized intensity of fluorescence (Le2)�, hereinbelow) is obtained pixel by pixel by dividing the value of each pixel of the narrow-band fluorescence image data (Le2) by the value of the corresponding pixel of the broad-band fluorescence image data (Le2), color information for each pixel is generated on the basis of the degree of influence of the disturbance factor for the pixel calculated from the normalized intensity of fluorescence (Le2) for the pixel, brightness information for each pixel is generated on the basis of the value of the corresponding pixel of the IR reflection image data, and a disturbance judgment image is displayed on the monitor 70 on the basis of combination of the color information and the brightness information.
The illumination unit 20 comprises a stimulating light source unit comprising a Ga�N semiconductor laser 201 which emits the stimulating light Le1 of a wavelength of 410 nm and a power source 202 for the semiconductor laser 201, a stimulating light source unit comprising a Ga�N semiconductor laser 204 which emits the stimulating light Le2 of a wavelength of 500 nm and a power source 205 for the semiconductor laser 204, and a reference light source unit comprising a semiconductor laser 207 which emits near-infrared light as the reference light Ls and a power source 208 for the semiconductor laser 207.
When taking a fluorescence image, the power source 202 is operated under the control of a signal from the controller 60 and the Ga�N semiconductor laser 201 radiates a stimulating light Le1 of a wavelength of 410 nm. The stimulating light Le1 enters the light guide 102 a through a lens 203, propagates to the front end of the scope section 10, and then is projected onto the object part 1 by the illumination lens 104.
The Ga�N semiconductor laser 204 radiates a stimulating light Le2 of a wavelength of 500 nm. The stimulating light Le2 enters the light guide 102 b through a lens 206, propagates to the front end of the scope section 10, and then is projected onto the object part 1 by the illumination lens 104.
Thereafter the Ga�N semiconductor laser 204 radiates a stimulating light Le2 of a wavelength of 500 nm. The stimulating light Le2 enters the light guide 102 b through a lens 206, propagates to the front end of the scope section 10, and then is projected onto the object part 1 by the illumination lens 104. A fluorescence image Zj2 emitted from the object part 1 upon exposure to the stimulating light Le2 is condensed by the condenser lens 105 to enter the image fiber 103. Then the fluorescence image Zj2 impinges upon the CCD image taking device 308 by way of the image fiber 103, the condenser lens 309, the optical filter 302 b of the variable stimulating light cut filter means 301, the optical filter 305 c of the variable filter means 304 and the condenser lens 307. The optical filter 302 b of the variable stimulating light cut filter means 301 cuts wavelengths not longer than 510 nm and the optical filter 305 c of the variable filter means 304 only transmits wavelengths of 530 nm to 800 nm. Accordingly, the components of the fluorescence image Zj2 in the wavelength band of 530 nm to 800 nm impinges upon the CCD image taking device 308.
B1={(NF2−Av2)/St2}2 Then the disturbance image generating section 408 allocates to the pixels color information on the basis of the degree of influence B1 of the disturbance factor (e.g., the disturbance image generating section 408 allocates pseudo-color to the pixels so that the color of the pixels varies from white to magenta as the degree of influence B1 increases), allocates to the pixels brightness information on the basis of the value of the IR reflection image data, generates disturbance judgment image data on the basis of combination of the color information and the brightness information and outputs the disturbance judgment image data to the video signal processing circuit 409. The video signal processing circuit 409 converts the disturbance judgment image data to a video signal and outputs the video signal to the monitor 70. The disturbance judgment image which is a pseudo-color image is displayed by the monitor 70.
In the fluorescence endoscope of this embodiment, stimulating light Le1 of a wavelength of 410 nm is projected onto the object part 1, a normalized intensity of fluorescence is obtained on the basis of fluorescence emitted from the object part 1 upon exposure to the stimulating light Le1 (This normalized intensity of fluorescence will be referred to as �the normalized intensity of fluorescence (Le1)�, hereinbelow), stimulating light Le3 of a wavelength of 360 nm is projected onto the object part 1, a normalized intensity of fluorescence is obtained on the basis of fluorescence emitted from the object part 1 upon exposure to the stimulating light Le3 (This normalized intensity of fluorescence will be referred to as �the normalized intensity of fluorescence (Le3)�, hereinbelow), whether each pixel 2 of the object part 1 is a clean tissue or an unclean tissue is judged on the basis of the normalized intensity of fluorescence (Le1) and the normalized intensity of fluorescence (Le3), color information for each pixel is generated on the basis of the result of the judgment, IR reflection image data is obtained on the basis of reflected reference light Ls (near-infrared light) reflected by the object part 1 when the reference light Ls is projected onto the object part 1, brightness information for each pixel is generated on the basis of the value of the corresponding pixel of the IR reflection image data, and a disturbance judgment/fluorescence diagnostic image (a pseudo-color image) is displayed on the monitor 70 on the basis of combination of the color information and the brightness information.
The illumination unit 21 comprises a stimulating light source unit comprising a Ga�N semiconductor laser 201 which emits the stimulating light Le1 of a wavelength of 410 nm and a power source 202 for the semiconductor laser 201, a stimulating light source unit comprising a Ga�N semiconductor laser 210 which emits the stimulating light Le3 of a wavelength of 360 nm and a power source 211 for the semiconductor laser 204, and a reference light source unit comprising a reference light source 207 which emits the reference light Ls and a power source 208 for the reference light source 207.
The power source 202 is operated under the control of a signal from the controller 61 and the Ga�N semiconductor laser 201 radiates a stimulating light Le1 of a wavelength of 410 nm. The stimulating light Le1 enters the light guide 112 a through a lens 203, propagates to the front end of the scope section 11, and then is projected onto the object part 1 by the illumination lens 104.
The image signal output from the CCD image taking device 117 is processed by the signal processing circuit 401, is digitized by the A/D convertor 402 and is stored in the image memory 411 divided into the narrow-band fluorescence image data (Le1) obtained through the optical filters 116 a and the broad-band fluorescence image data (Le1) obtained through the optical filters 116 c. Then the power source 212 is operated under the control of a signal from the controller 61 and the Ga�N semiconductor laser 211 radiates a stimulating light Le3 of a wavelength of 360 nm. The stimulating light Le3 enters the light guide 112 b through a lens 213, propagates to the front end of the scope section 11, and then is projected onto the object part 1 by the illumination lens 104.
B2={(NF3−Av3)/St3}2 Though, in the second and third embodiments, the mosaic filter 115 comprises optical filters 116 a transmitting light in a wavelength band of 430 nm to 530 nm, optical filters 116 b transmitting light in a wavelength band of 430 nm to 490 nm, optical filters 116 c transmitting light in a wavelength band of 430 nm to 700 nm, and optical filters 116 d transmitting light in the entire wavelength band, the optical filters transmitting light in a wavelength band of 430 nm to 530 nm may be caused to double as the optical filters transmitting light in a wavelength band of 430 nm to 490 nm and the optical filters transmitting light in the entire wavelength band may be caused to double as the optical filters transmitting light in a wavelength band of 430 nm to 700 nm. In this case, the mosaic filter may comprise only two kinds of optical filters, which results in improvement of resolution and increase in amount of detected fluorescence.
The fluorescence endoscope of the fourth embodiment comprises, as shown in FIG. 8, a scope section 13 which is inserted into a suspected diseased part of a patient, an illumination unit 23 provided with sources of the stimulating light Le1 of a wavelength of 410 nm, the stimulating light Le3 of a wavelength of 360 nm, the reference light Ls, and the red light Lr, green light Lg, and blue light Lb projected onto the object part 1 in sequence in order to take an ordinary color image (will be referred to as �the sequential light�, hereinbelow), an ordinary image processing unit 33 which outputs ordinary image data, a fluorescence image processing unit 43 which calculates the normalized intensity of fluorescence (Le1) on the basis of the narrow-band fluorescence image data (Le1) and the broad-band fluorescence image data (Le1) and outputs fluorescence diagnostic image data on the basis of the normalized intensity of fluorescence (Le1) and the IR reflection image data, an optical path separating unit 50 which separates the optical path of the stimulating light Le3 and the optical path of the detected fluorescence, a disturbance calculation unit 51 which outputs the degree of influence B3 of the disturbance factor calculated on the basis of the normalized intensity of fluorescence F1/F2 and reference values which have been stored, a controller 63 which is connected to the units and controls the timing of operation of the units, the input system 631 connected to the controller 63, the monitor 70 and the quartz fiber 53 which propagates the stimulating light Le3 and fluorescence emitted from the pixels 2 of the object part 1 upon exposure to the stimulating light Le3.
The illumination unit 23 comprises a stimulating light source unit comprising a Ga�N semiconductor laser 201 which emits the stimulating light Le1 of a wavelength of 410 nm and a power source 202 for the semiconductor laser 201, a stimulating light source unit comprising a Ga�N semiconductor laser 211 which emits the stimulating light Le3 of a wavelength of 360 nm and a power source 212 for the semiconductor laser 204, a reference light source unit comprising a reference light source 207 which emits the reference light Ls and a power source 208 for the reference light source 207, and a sequential light source unit comprising a white light source 231, a power source 232 for the white light source 231, a color switching filter 234 for separating red light Lr, green light Lg and blue light Lb from white light in sequence, and a filter drive system 236 which rotates the color switching filter 234.
The optical path separating unit 50 comprises a dichroic mirror 501 which causes the stimulating light Le3 radiated from the Ga�N semiconductor laser 213 to enter the quartz fiber 53 and causes fluorescence propagated through the quartz fiber 53 to enter the disturbance calculation unit 51.
When the fluorescence diagnosis mode is selected, the power source 202 is operated under the control of a signal from the controller 63 and the Ga�N semiconductor laser 201 radiates a stimulating light Le1 of a wavelength of 410 nm. The stimulating light Le1 enters the light guide 132 a through a lens 203, propagates to the front end of the scope section 10, and then is projected onto the object part 1 by the illumination lens 104.
When the pixel 2 displayed in red cannot be determined whether it is a clean diseased tissue or an unclean tissue on the fluorescence diagnostic image, the viewer leads the front end of the quartz fiber 53 near to the object part 1 and switches the endoscope to the disturbance measurement mode by the input system 631. When the disturbance measurement mode is selected, the power source 212 is operated under the control of a signal from the controller 63 and the Ga�N semiconductor laser 211 radiates a stimulating light Le3 of a wavelength of 360 nm. The stimulating light Le3 passes through a lens 213 and impinges upon the dichroic mirror 501. The stimulating light Le3 is reflected by the dichroic mirror 501 and enters the quartz fiber 53 through a lens 502. Then the stimulating light Le3 is projected onto the object part 1 from the front end of the quartz fiber 53.
B3={(NF3−Av3)/St3}2 Further, the fluorescence diagnostic information generating section 520 outputs the calculated degree of influence B3 of the disturbance factor to the monitor 70 and the monitor 70 displays the calculated degree of influence B3 of the disturbance factor in numeric representation. That is, when the value of the degree of influence B3 of the disturbance factor is small, the pixel 2 may be considered to be clean and when the value of the degree of influence B3 of the disturbance factor is large, the pixel 2 may be considered to be unclean.
The illumination unit 24 comprises a stimulating light source unit comprising a Ga�N semiconductor laser 201 which emits the stimulating light Le1 of a wavelength of 410 nm and a power source 202 for the semiconductor laser 201, a stimulating light source unit comprising a Ga�N semiconductor laser 204 which emits the stimulating light Le2 of a wavelength of 500 nm and a power source 205 for the semiconductor laser 204, a reference light source unit comprising a reference light source 207 which emits the reference light Ls and a power source 208 for the reference light source 207, and a sequential light source unit comprising a white light source 231, a power source 232 for the white light source 231, a color switching filter 234 for separating red light Lr, green light Lg and blue light Lb from white light in sequence, and a filter drive system 236 which rotates the color switching filter 234.
When the disturbance measurement mode is selected, the power source 205 is operated under the control of a signal from the controller 64 and the Ga�N semiconductor laser 204 radiates a stimulating light Le2 of a wavelength of 500 nm. The stimulating light Le2 passes through a lens 203 and impinges upon the dichroic mirror 501. The stimulating light Le2 is reflected by the dichroic mirror 501 and enters the quartz fiber 53 through a lens 502. Then the stimulating light Le2 is projected onto the object part 1 from the front end of the quartz fiber 53.
B4={(F3/F4−Av4)/St4}2 Further, the fluorescence diagnostic information generating section 547 outputs the calculated degree of influence B4 of the disturbance factor to the monitor 70 and the monitor 70 displays the calculated degree of influence B4 of the disturbance factor in numeric representation. That is, when the value of the degree of influence B4 of the disturbance factor is small, the pixel 2 may be considered to be clean and when the value of the degree of influence B4 of the disturbance factor is large, the pixel 2 may be considered to be unclean.
Av−St<NF<Av+St Though, in the fourth and fifth embodiments, the mosaic filter 135 comprises optical filters 136 a transmitting light in a wavelength band of 430 to 530 nm, optical filters 136 b transmitting light in a wavelength band of 430 nm to 700 nm, and optical filters 136 c transmitting light in the entire wavelength band, the optical filters transmitting light in the entire wavelength band may be caused to double as the optical filters transmitting light in a wavelength band of 430 nm to 700 nm. In this case, the mosaic filter may comprise only two kinds of optical filters, which results in improvement of resolution and increase in amount of detected fluorescence.
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Cited by examinerClassifications U.S. Classification250/461.1International ClassificationA61B1/00, G01N21/64, A61B5/00Cooperative ClassificationA61B5/0086, A61B5/0071, A61B5/0084European ClassificationA61B5/00P12B, A61B5/00P12B2, A61B5/00P5Legal EventsDateCodeEventDescriptionFeb 6, 2014FPAYFee paymentYear of fee payment: 8Jan 29, 2010FPAYFee paymentYear of fee payment: 4Feb 15, 2007ASAssignmentOwner name: FUJIFILM CORPORATION, JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:FUJIFILM HOLDINGS CORPORATION (FORMERLY FUJI PHOTO FILM CO., LTD.);REEL/FRAME:018904/0001Effective date: 20070130Owner name: FUJIFILM CORPORATION,JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:FUJIFILM HOLDINGS CORPORATION (FORMERLY FUJI PHOTO FILM CO., LTD.);US-ASSIGNMENT DATABASE UPDATED:20100203;REEL/FRAME:18904/1Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:FUJIFILM HOLDINGS CORPORATION (FORMERLY FUJI PHOTO FILM CO., LTD.);US-ASSIGNMENT DATABASE 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