CA2067188C - Multi-color laser scanning confocal imaging system - Google Patents
Multi-color laser scanning confocal imaging system Download PDFInfo
- Publication number
- CA2067188C CA2067188C CA002067188A CA2067188A CA2067188C CA 2067188 C CA2067188 C CA 2067188C CA 002067188 A CA002067188 A CA 002067188A CA 2067188 A CA2067188 A CA 2067188A CA 2067188 C CA2067188 C CA 2067188C
- Authority
- CA
- Canada
- Prior art keywords
- light
- laser
- excitation
- lines
- stains
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
- G02B21/0004—Microscopes specially adapted for specific applications
- G02B21/002—Scanning microscopes
- G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
- G02B21/0052—Optical details of the image generation
- G02B21/0076—Optical details of the image generation arrangements using fluorescence or luminescence
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
- G02B21/0004—Microscopes specially adapted for specific applications
- G02B21/002—Scanning microscopes
- G02B21/0024—Confocal scanning microscopes (CSOMs) or confocal "macroscopes"; Accessories which are not restricted to use with CSOMs, e.g. sample holders
- G02B21/0052—Optical details of the image generation
- G02B21/0064—Optical details of the image generation multi-spectral or wavelength-selective arrangements, e.g. wavelength fan-out, chromatic profiling
Abstract
A true multi-color laser scanning confocal imaging system for use with a microscope is described in which a single laser having a multi-line output is used to simultaneously or individually excite a plurality of dyes. The images may be simultaneously viewed by a plurality of photomultiplier tubes to reconstruct an image showing distinct features of a specimen stained with different dyes. The images may also be constructed using a single detector is a time-multiplex fashion and using a computer to construct the image.
Description
.,.. ~~, _1_ LASER FOR CONFOCAL MICROSCOPE
~~ 206188 Field of the Invention The present invention relates to confocal microscopy and in particular to laser scanning confocal microscopy in which laser light is used to excite dyes in a specimen.
Background of the Invention Confocal microscopy is well known in the art.
The concept of confocal microscopy is that the image viewed by the microscope is confined to a very precise ' .. focal plane by limiting the depth of field of the image.
Only those portions of the specimen which are in focus are detected. Out of focus regions of the sample appear dark. By changing the position of the focal plane, this important principle defines one major method for achieving optical sectioning.
The earliest versions of confocal microscopes used direct vision design with incoherent illumination.
The field of illumination in the specimen was limited by a pin hole positioned on the illumination axis. The image of this pin hole is then projected on the specimen by a condenser lens. The illuminated point on the specimEn reflects light (or as described below, emits fluorescent light). The reflected light of the image is then focused through an objective lens onto a detector.
Either the specimen or the light focused on the image is scanned in a raster pattern so that the detector collects pixel information from a region of the specimen. The pixel information is then passed through a computer which a .:
can generate an image of the overall specimen.
iY'.'.
r:', _ The concept of the scanning confocal microscope is described in US Patent 3,013,467 to Marvin Minsky, which is hereby incorporated by reference. The optical path of the scanning confocal microscope may be constructed in trans-illuminating mode in which a =:.~, separate condenser and objective lens is used in the same y. axis. In the alternative, the optical path of the ,,, ' WO
v, P~ w 6~~~~ -2- .
, , '.J '..
scanning confocal microscope may be constructed in an epi-illuminating mode making a single objective lens , serve both as the condenser and objective lens and using a dichroic or half mirror to collect the emitted light , . 5 into a detector, as shown in Figure 1.
In the Minsky patent, the raster scan is generated by moving the stage on which the specimen is supported by two orthogonally vibrating tuning forks that w are driven by electromagnets. As the stage is moved in a .
raster scan pattern, the resulting image detected by the ., image detector is a serial raster scanned image.
. The use of fluorescent dyes to stain the specimen being viewed further improved the range of applications to which scanning confocal microscopy could be applied. Especially in the area of immunofluorescence histochemistry and in other neuroanatomical techniques, ., the staining of specimens with dyes is particularly useful to aid in distinguishing different features within biological tissues. The stains may comprise dyes designed only to absorb light or dyes that emit light in response to absorption, which is called fluorescence.
Fluorescent dyes have the advantage over dyes which only absorb light in that a given fluorescent marker will be visible only when illuminated with the appropriate filter set.
Fluorescence is a consequence of the .,, interaction of a photon with a fluorophore. When a '' .y photon of light is absorbed by a molecule it may increase the potential energy of the molecule by raising an electron to a higher orbital state. An electron raised to a higher orbital state from its natural state will 'v' tend to revert to the natural state. When the electron a.- :.
falls from a higher to a lower orbital state, energy is .. released which is equal to the difference in energy .. 35 between the two orbital states. When this occurs, part or all of its energy may be released as a photon having a <.~;,~ .
o.~i;; . . . .
-3- . v206,"~188 j . wavelength (spectral line) proportional to the released energy. The resulting luminescence is called fluorescence (and in some circumstances phosphorescence).
Excitation of a fluorophore molecule at one wavelength typically results in fluorescent emission at longer . wavelengths of light.
The scanning laser confocal microscope improved y on the design of the scanning confocal microscope and the use of fluorophores by using coherent light to scan the stained specimen. The monochromaticity, high intensity and lack of divergence of the laser light contributed to improvements in the resulting images. In an epi-illuminating laser scanning confocal microscope of the ' prior art, as shown in Figure 2, the laser light 200 is scanned onto the specimen 220 from above and is reflected to a detector 215 in the same focal path as the incident light through the use of a half mirror or dichroic mirror 205. Typically, the specimen is stained with fluorescent dyes to enhance specific features within the specimen which may be of interest.
The MRC-600 laser scanning confocal imaging system, shown diagrammatically in Figure 2, is manufactured by BioRad Microscience of Hemel Hempstead, Herts, England. This laser scanning confocal microscope system is adaptable for use with a number of upright and inverted microscopes available from microscope vendors such as Nikon, Zeiss, Olympus and Leitz. The coherent illumination is an argon ion laser 201 having primary lines at 514 and 488 manometers (nm). The emitted laser light 200 also has a plurality of minor spectral lines as determined by argon. The lines are filtered by the external filter 203 which selects either the 488nm (blue) line the 514nm (green) line by means of an excitation filter 203. The selected light is reflected by a beam splitter 205 which includes a dichroic mirror used for fluorescent imaging. If simple reflection imaging is ~' ~ :~ ~ ~~
.. . Q ~' _4_ required, a semi-reflecting or half mirror may be used in place of the dichroic mirror 205.
The argon ion laser is available from Ion Laser Technology Company of Salt Lake City, Utah, part number , 5425A. The argon ion laser is used to excite yluorescent dyes in the specimen which emit light slightly shifted in the spectrum in response to the excitation wavelength of the spectral lines of the laser light. The dyes are selected based upon their sensitivity to light, their ", 10 affinity for features desired to be viewed in specimens and their fluorescent capabilities.
The light 200 from the laser is passed through the scanning unit 207 where it is raster scanned in an XX
scanning movement by means of two oscillating mirrors.
The laser beam is then passed through a microscope eyepiece onto the specimen such that a scanning spot caused by the scanning unit 207 scans the specimen.
Reflected light or fluorescent light from the specimen passes back through the scanning system along the same path as the incident laser light. Reflection of the light is so rapid that the mirrors have not shifted ' position so that the light retraces the exact original path in the reverse direction. A portion of the reflected or fluorescent light.passes through a half ..::
mirror or dichroic mirror 205 to be passed to photomultiplier tubes.
The laser scanning confocal imaging system from BioRad shown in Figure 2 attempts simultaneous imaging of two different fluorescent stains. The 514nm spectral line from argon ion laser 201 is used to excite both fluorescein isothiocyanate (fluorescein) and Texas Red"
(from Molecular Probes, Inc.) conjugated probes. This attempts the simultaneous excitation of different fluorescent dyes to allow selected features of the specimen to be stained in different colors and viewed together. The dual images are picked up by ~;.,.
-5- ~ 2067188 photomultiplier tubes 213 and 215. A second beam splitter 207 is a dichroic mirror allowing light of one wavelength to be directed to photomultiplier tube 213 while light having other wavelengths passed to photomultipiiar 215.
w' The two images received from photomuitiplier tubes 213 and 215 are used by a computer 222 to construct an image on display 224 of the specimen in a single focal plane. The simultaneous imaging of two different fluorescent stains at exactly the same focal plane would ';, allow the identification of different specific features in the same specimen. A shortcoming of the dual color laser scanning confocal microscope system of the prior art is that the 514nm line of the argon ion laser produces simultaneous excitation of the two fluorescent dyes (fluorescein and Texas Red~). This simultaneous excitation causes false imaging and the loss of feature ,, detail in the resulting image generated by the computer.
Figure 3 shows a graph published by BioRad Microscience indicating the absorption and emission >.:~> ' spectra of fluorescein and Texas Red'. The graph is reproduced from BioRad and only approximates the spectrums. Curve 301 describes the absorption spectra of fluorescein while curve 303 shows the emission spectra of fluorescein. Curve 305 shows the absorption spectra of Texas Red'M and curve 307 describes the emission spectra of Texas Red''. As can be seen in Figure 3, there is an ., area of overlap between the absorption spectrums of Texas Red"~ and fluorescein at 514nm. Thus, simultaneous excitation and emission of fluorescein and Texas Red'' occurs when excited with the single 514nm line of the argon laser. Also shown in Figure 3 is a large area of overlap between the emission spectra of Texas Red'T' and the emission spectra of fluorescein.
The response curves for the filters and the dichroic reflectors are placed below the absorption and ~~'~$$ - 6 - .;,,~, emission spectra of fluorescein and Texas Red'T' in Figure 3 for comparison. .i~hen using an argon laser to excite , the dyes, the 514nm line of the dye is the only line allowed to pass through the exciter filter 203 shown in Figure 2. The narrow wavelength response curve 309 of Figure 3 is for the exciter filter 203. The response curve 311 is for dichroic reflector 205 and the response curve 313 is for dichroic reflector 207. The response curve 315 is for green channel filter 211 and the IO response curve 317 is for red channel filter 209.
As can be seen in Figures 3, the intent is to have the single 514nm line of the argon laser excite both w the fluorescein and Texas Red"' dyes. The emission spectra of these respective dyes are then selected to be passed to photomultiplier tubes 213 arid 215 shown in Figure 2 to be independently detected for reconstructing a two color image at the same focal plane. The problem .17 with this prior art technique is that the single excitation line from the argon laser excites fluorescein ~?, 20 much more efficiently than Texas Red. For example, as w;.,,shown in Figure 3, the excitation of the fluorescein dye at a wavelength of 514nm is at approximately 50%. The excitation of Texas Red"" at the same 514nm wavelength, ., however, is very low (less than 3%). Since the emission spectra of the dyes corresponds to, and is proportional to the amount of energy absorbed by the dyes, the low amount of absorbed energy from the 514nm line by Texas Red'1° will result in a very low amount of emitted .; fluorescent light. Hence, the amount of fluorescein emission seen in the red channel can vary according to the relative concentrations of fluorescein and Texas Red's. Unless the relative concentrations and saturation of the dyes accurately controlled, the emission spectra of Texas Red's may be swamped by the "spillover" of the longer wavelengths of the fluorescein emission spectra.
This confusion will result in images in which many of the x«°:3, _7_ ~ 206y.~88 features stained only with fluorescein will appear in both images. One solution to this problem is to use separate laser lines to better excite both fluorescent dyes.
Multiple line excitation of specimens dyed with different fluorochromes using two lasers is also known in the prior art. For example, a Spectra-Physics 2025 argon ' ion 3-watt water cooled laser (tunable to a single argon ion line between 351nm through 528nm) has been confocally aligned with a 5 milliwatt air-cooled argon ion laser having fixed wavelengths at 488nm and 514nm. The alignment of two lasers, however, presents extreme focusing problems. The two light paths must be aligned to exacting standards to ensure that the same focal plane is observed.
Summary of the Invention The shortcomings of the prior art described . above and other shortcomings of the prior art which will be recognized and understood by those skilled in the art upon reading and understanding the present specification are overcome by the present invention. The present invention teaches a true multi-color laser scanning confocal imaging system for use-with a microscope in which a single laser having a multi-line output is used to simultaneously or individually excite a plurality of dyes. The images may be simultaneously viewed by a plurality of photomultiplier tubes to reconstruct an image showing distinct features of a specimen stained with different dyes. The images may also be constructed using a single detector in a time-multiplex fashion and using a computer to construct the image.
:,.~~~ ;
~~~,,:.. -8-., Description of the Drawinas In the drawings where like numerals refer to .
bike components throughout the several views, Figure l~is a diagram showing a prior art optical confocal microscope system.
Figure.2 is ~a diagram showing a prior art laser , '. scanning confocal imaging system.
Figure 3 shows the response spectra of the' . various components of Figure 2.
Figure 4 shows a typical layout of the various ;y components for the present invention. w ''~' Figure 5 is a diagram showing a two-color optical confocal microscope system using two detectors.
Figure 5a shows the response spectra of the ' 15 various components of Figure 5.
V'''''' Figure 6 is a diagram showing a time-multiplex single detector laser scanning confocal imaging system.
Figure 7 shows the absorption and emission spectra of various fluorochromes.
Figure 8 shows the response spectra of the various filters and dichroic reflectors used in the time-multiplex single detector laser scanning confocal imaging system of Figure 6.
Figure 9 is a diagram showing a multi-detector, multicolor optical confocal microscope system using three detectors.
Detailed Description of the Preferred Embodiment In the following detailed description of the preferred embodiments, references made to the accompanying drawings which form a part hereof and in which is shown by way of illustration specific embodiments in which the invention may be practiced.
These embodiments are described in sufficient detail to enable those skilled in the art to practice the invention, and it is to be understood that other ~
_9_ ~os~y g~~=:
embodiments may be utilized and that structural or physical changes may be made without departing from the spirit and the scope of the present invention. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope of the present invention is defined by the appended claims.
Figure 4 shows a typical layout of the various components for the present invention. The layout is similar to that of the MRC-600 laser scanning confocal -imaging system manufactured by BioRad Microscience Ltd.
of Hemel Hempstead, Herts, England. The present laser scanning confocal microscope system is also adaptable for ."~'r' use with a number of upright and inverted microscopes available from microscope vendors such as Nikon, Zeiss, . 15 Olympus and Leitz. The main optics and scanner head of the present invention are housed cabinet 401. The source of laser light 403 is supported near the cabinet so that the mufti-line laser light enters the cabinet. In the configuration shown, the incident laser light exits the cabinet to enter the microscope 405 from the top. The reflected of emitted light is received from the microscope along the same optical path as the incident laser light.
Cabinet 401 also contains the detectors, which in the preferred embodiments are photomultiplier tubes.
Those skilled in the art will readily recognize that other detectors may be used such as CCD devices, vidicon tubes, etc. The detectors within the cabinet and the scanners are connected to computer 407 which constructs the images of the specimen and displays them on display 409.
Figure 5 is a schematic diagram of a basic two-color imaging system of a preferred embodiment of the invention. The scanning unit and other mirrors (described more fully below) of the scanning confocal microscope shown in Figure 5 have been omitted for ~ PCT/US91/00607 ~,o . -lo-clarity. Figure 5a is a series of graph depicting the ,,; spectral response curves for the components of Figure 5.
Figures 5 andw5a should be viewed together. The laser .. light source 501 is an air-cooled krypton/argon ion laser, Model No: 5470-KBR, available from Ion Laser ':. Technology in Salt Lake City, Utah. This laser produces dominant spectral lines at 488nm, 568nm, and 647nm. The design of this laser suppresses other minor lines to ensure the emission of only the 488nm, 568nm, and 647nm .
lines. As will be described more fully below, other lasers may be used and other selected lines of laser light may be used to implement the preferred embodiments of the present invention without departing from the spirit and the scope of the claims.
The laser light 500 is filtered through excitation filter block 503. Excitation filter block 503 . contains a plurality of filters selectable by the user.
The filter shown selected is 503a, which is a dual bandpass filter allowing the passage of light at both 488nm and 568nm. Response curves 553a and 553b of Figure 5 describe the spectral response of dual band filter 503a. The selection of two lines from laser 501 allows for the excitation of two dyes in the specimen. Response curves 551 and 552 of Figure 5a correspond to filters 503b and 503c, respectively. Filters 503b and 503c may be used to individually select the 488nm or 568nm lines, respectively, from laser 501.
The filtered laser light is then passed to a dual dichroic filter block 505. The dual dichroic filter block is selected to reflect both the 488nm and the 568 nm lines. It is also selected to transmit from 500-540 nm for the fluorescent light emitted from fluorescein, and 585-650nm for the fluorescent light emitted from ' Texas Red'. Response curve 555 of Figure 5 depicts the spectral response of dichroic mirror 505.
CVO 92/02839 PC'T/US91/00607 ~:~.a ' , ;.;
..
The excitation of fluorescein causes the dye to emit light at a shifted wavelength with a longer wavelength than the excitation light. The incident laser light with lines at 488nm and 568nm is directed onto the specimen 507. The specimen has been stained with . fluorescein and Texas Red~ conjugated probes to highlight features of the specimen. The emitted light from the .' dyes follows the same path as the excitation laser light and strikes dual dichroic filter block 505. As described above, this filter block 505 has been selected to pass light in the wavelength of 500-540nm for fluorescein, and 585-650nm for Texas Red"". Response curve 555 of Figure 5 shows the dual bandpass spectral response of dichroic mirror 505.
The emitted light strikes several reflectors shown generally as reflect~.~r 509, which directs the light to a second filter block 511. Filter block 511 includes a second dichroic mirror 521, which passes light in the 585nm-650nm range and reflects light in the 500nm-540nm range. Response curve 561 of Figure 5 shows the spectral response of dichroic mirror 521. Photomultiplier tube 513 receives and detects emitted light passed from dichroic mirror 511 and filtered through low pass filter 515. Filter 515 is, in the preferred embodiment, a 585 LP long pass filter available from Omega. Response curve 562 of Figure 5 shows the spectral response of filter 517. Photomultiplier tube 513 is connected to a computer (not shown in this diagram) where the information is used to construct an image in the selected focal plane on the specimen 507. The scanning head is also not shown in Figure 5 for brevity of discussion.
Light reflected from filter block 511 in the 500-540 nanometer range is passed through filter 517, which in the preferred embodiment is a bandpass filter 522 DF 35 available from Omega. Response curve 563 of Figure 5 shows the spectral response of filter 515.
The CVO 92/02839 ~ PCT/US91 /00607 6'1~.$ .
passed light is detected by photomultiplier tube 519.
The detected information is then sent to the same computer connectedvto photomultiplier tube 513, where a second image representative of the features stained with fluorescain in specimen 507 is created by the computer.
The image detected by photomultiplier tube 513 represents features stained with the dye Texas Red'. The images formed by the computer detected by the two photomultiplier tubes are in the exact focal plane, since the same laser light beam is used to scan the same focal plane of the specimen without moving any parts. Thus, a true multi-color simultaneous imaging system is constructed where dyes are individually excited by different lines from the same laser.
Excitation filter block 503 contains band pass .. filters 503b and 503c for individual selection and viewing of stained areas corresponding to fluorescein and Texas Red'. Since the filter blocks containing the dichroic mirrors are not moved when switching excitation filters, the resulting images are perfectly aligned with respect to the focal plane. Thus, the user can select single color or a perfectly aligned multi-color image to be constructed by the computer.
Those skilled in the art will readily recognize that the excitation of dyes by the krypton/argon laser 501 is facilitated by the selection of the spectral lines of the laser light. Those skilled in the art will readily recognize that a krypton laser having dominant lines at 476/482nm, 520nm, 568nm and/or 647nm may be used to excite selected dyes and obtain results similar to those described above in conjunction with Figure 5.
Thus, a krypton laser with minor adjustments made to the filters and dichroic mirrors will produce acceptable ._ results useable with the present invention.
Figure 6 shows a multi-color, single-detector scanning laser confocal imaging system of an alternate WO 92102839 PCf/US91/00607 t ~.: ~:.
-13- , , ,~ e~:
J
preferred embodiment of the present invention. The multi-color images are serially constructed from a single detector by time-multiplex gathering of information by the computer. The laser selected for use in this embodiment is also an air-cooled krypton/argon ion laser, Model 5470-KBR available from ILT. Those skilled in the ', art will readily recognize that, by appropriate selection of filters and dichroic mirrors, other lasers, such as a krypton laser could be used with the present invention as described in conjunction with Figure 6, such as an air-cooled krypton laser, Model 5470K available from Ion Laser Technology. Other vendors produce lasers which would be acceptable with the present invention.
Krypton/argon ion laser 601 produces dominant spectral lines at 488nm, 568nm, and 647nm. Table 1 ",: describes the selection of filters and mirrors to be used with the krypton/argon laser. In the construction of the preferred embodiment of the present invention described in conjunction with Figure 6, the excitation filter 607, the dichroic mirror 609 and the emission filter 611 are all mounted together in a single filter block 605.
In this fashion, matched sets of these filters may be easily substituted without disturbing the other optics by merely r eplacing the filter blocks 605.
Filter Laser Excitation Dichroic Emission Block Line Filter Mirror Filter Blue 488 nm 488 DF 10 500 DCLP 522 DF 35 Yellow 568 nm 568 DF 10 585 DCLP 600 DF 20 Red 647 nm 647 DF 10 660 DCLP 665 LP
The krypton gas of the laser produces spectral lines . at 476/482nm, 520nm, 568nm and 647nm, among others. The argon gas produces spectral lines at 488nm and 514nm, among 'i a .. s others. The krypton/argon laser is designed to suppress all lines except those at 488nm, 568nm and 647nm. Since the 488nm line from. the argon gas excites fluorescein more efficiently,~the mixed gas krypton/argon laser is preferred.
Those skilled in the art will readily recognize, however, that adequate power from the 476/482nm line of a krypton can excite fluorescein for use in the present invention. Hence, a krypton laser may be substituted for use with the present invention with the appropriate matching filters and dichroic mirrors.
The preferred krypton/argon laser from ILT is air-cooled since it is inexpensive and easily cooled. Since liquid or water-cooled lasers suffer much vibration due to the pumping of the liquid around the tube for coolant, air-cooled lasers are preferred. Air-cooled lasers, of course, are also preferred because of the cost differential between air-cooled and water-cooled high-powered lasers.
Referring once again to Figure 6, the specimen 603 is dyed with three dyes: fluorescein, Lissamine rhodamine (or Texas Red'"'), and cyanine 5.18. These dyes can be excited by the laser lines described for the krypton/argon laser and be detected by the photomultiplier tube without interference from the other dyes. In some cases, however, higher light levels for the cyanine 5.18 dye may be required due to the lower sensitivity of the photomultiplier tube to red light.
Figure 7 should be viewed in conjunction with an explanation of laser 601 of Figure 6. Figure 7 shows a graph of the absorption spectra and emission spectra of selected ., dyes which may be used to stain specimen 603 of Figure 6.
.. . , The graph of Figure 7 shows the spectra curves normalized on a scale of zero to one hundred as a measure of relative -intensity to one another. Curve 701 corresponds to the absorption spectra of fluorescein and curve 703 corresponds to the emission spectra of fluorescein. Curve 705 corresponds to the absorption spectra of Lissamine rhodamine and curve 709 corresponds to the emission spectra of WO 92/02839 ; PCT/US91/00607 ".
-15- ~ 20671188 Lissamine rhodamine. Curve 711 corresponds to the absorption spectra of cyanine 5.18 and curve 713 corresponds to the emission spectra of cyanine 5.18. tdith proper selection of .. , excitation light, the emission and absorption spectra of the various selected dyes are sufficiently removed to allow filtering and detection by separate photo multiplier tubes as v shown in Figure 6.
Figure 8 is a description of the response of the various filters of Figure 6. The response curves are described as being part of one of three filter blocks: blue, yellow and red. Response curve 801 corresponds to the response curve of a 488 emission filter Part No. 488 DF10 available from Omega Instruments, Inc. Curve 803 is the dichroic mirror 500 DCLP long pass filter available from Omega. Response curve 805 corresponds to emission filter 522 DF 35 available from Omega. Response curves 801, 803 and 805 are part of the blue filter block.
For the yellow filter block, response curve 807 corresponds to the 10 nanometers wide emission filter Part No. 568 DF 10. Curve 809 corresponds to dichroic mirror ,., Part Nc. 585 DCLP available from Omega. Curve 811 :w5.; .
corresponds to the emission filter Part No. 600 DF 20 also available from Omega.
The red filter set corresponds to curves 813, 815 and 817. Curve 813 is the response curve for the excitation filter Part No. 647 DF 10. Curve 815 corresponds to the long pass dichroic mirror filter 660 DCLP available from Omega.
Curve 817 corresponds to the emission filter which is a long pass filter 665 LP also available from Omega.
Referring once again to Figure 6, a time-multiplexed, three-colored confocal microscope is implemented by changing the filter blocks 605 corresponding to the colors desired to be viewed in the specimen 603. The filter block 605 comprised of excitation filter 607, the dichroic mirror 609 and the emission filter 609 are all changed together to w'. correspond to the specific dye being viewed. The multi-WO 92/02839 ~~ PCT/US91/00607 ~~~~; i: i . . _ -16-spectral line laser light 600 from laser 601 enters the . selected excitation filter 607 which narrowly selects one of , the available laser lines from the krypton/argon laser. The laser light with the selected line is reflected by preselected dichroic mirror 609 which corresponds to the selected line.
Dichroic mirror 609 will reflect the laser light containing the selected line onto the XY scanning unit 613 which causes the laser beam to be raster scanned on the specimen. XY scanning unit 613 is available within the BioRad Microscience MRC-600 confocal imaging system. The scanning unit 613 contains two mirrors which are connected to galvanometers which move the mirrors at selected scanning . , rates. One of the mirrors is responsible for generating an X
axis scan while the other mirror produces a Y axis scan. The scanning is synchronized to the receipt of images by the photomultiplier tubes and the generation of computer images ,, by means of a scan card and frame store in the computer 620.
The scanned laser light containing the laser line of interest is projected through the microscope objective onto specimen 603. The dye corresponding to the selected laser line fluoresces and emits a longer wavelength light in response to the excitation. The longer wavelength emitted light is passed back along the same optical path through scanning unit 613 to dichroic mirror 609. The longer wavelength emitted light passes through dichroic mirror 609 to emission filter 611. The emission filter is selected from the group described above~corresponding to the selected laser y:~; 30 line and dye to be viewed.
The emitted light through filter 611 is passed to the photomultiplier tube 615 where the scanned image is received, converted to electrical images and passed to the computer 620. The computer 620 reconstructs the image for ., . 35 the particular dye being excited by the selected line.
:~!7 ,r J hJ
-17- ~ 20fi'~~.88 This process is duplicated for each of the colors desired to be viewed. The filter block 605 containing filters 607, 611 and dichroic mirror 609 can be easily changed without disturbing the alignment of the laser, the specimen or the photomultiplier tube. The specimen can then be scanned with the filter block for the second dye.
However, by changing filter blocks, the region on the focal plane scanned may shift slightly in the XY plane due to the small differences in the angle of the dichroic mirrors in the .
filter blocks. After acquiring the images, the computer can combine and align the two images to produce a true two-color or pseudo color image. Quite often a pseudo color image is created wherein one color on the computer generated image . corresponds to a detected color from the specimen. The color detected from the specimen may not correspond to the color used by the computer to highlight the features stained by that particular dye since it may be more aesthetically pleasing to view higher contrasting colors than the actual colors received from the specimen.
.
In addition, the filter block 620 may be replaced by the third filter set and a third color scanned and combined with the previous two images to generate a true three-colored ,. image by computer 615.
Figure 9 shows a true three-color laser scanning confocal microscope which does not require the substitution of filter blocks to generate a three-color image. With the embodiment shown in Figure 9, a simultaneous three-color image may be scanned in which all three laser lines excite the dyes simultaneously. Laser 601 is a krypton/argon laser E, as described above. The multi-line laser light 600 passes through a broad-bandpass filter 907 where it is reflected by multi-passband dichroic mirror 909. The laser excitation light 600 is raster scanned by scanning unit 913 and enters the microscope eyepiece.
The specimen 603 is stained with dyes as described above which fluoresce when excited. The emitted light follows the WO 92/02839 ~~~ PGT/US91/00607 . , . ., ,; y , , . -18 - . ,.
same optical path followed by the excitation J.aser light through the scanning unit 913. The emitted light has a longer wavelength than the excitation light and passes through multi-passband dichroic mirror 909. The emitted light then strikes a second dichroic mirror 917 selected to ;,; reflect blue light and pass the other colors.
Photomultiplier tube 915 receives blue light emitted by fluorescein as filtered by emission filter 607.
The longer wavelength emitted light has passes through the second dichroic mirror 917 where it strikes a third dichroic mirror 919 selected to reflect red light and pass longer wavelength red light. Photomultiplier tube 921 receives red light emitted by Lissamine rhodamine (or Texas Red"~~ as filtered by emission filter 925. Photomultiplier tube 923 receives longer wavelength red light emitted by cyanine 5.18.
Fluorescein conjugated probes are one of several dyes available for use in conjunction with the preferred embodiments of the present invention in staining specimens .: ..
and examining selected features. Table 2 describes a number of dyes that may be used with the present invention.
i.: .::
~
.:
-19- ~ ~ ..:~. p.6'~ 18 8 Fluorescent Dyes for Con~uaation Fluorescein isothiocyanate ~FITC) Borate-dipyrromethane ("Bodipy) Lucifer Yellow Tetramethylrhodamine isothiocyanate (TRITC) Lissamine rhodamine Texas Red'" (from Molecular Probes, Inc.) Allophycocyanine Ultralite T-680"' (Ultra Diagnostics Corp, Seattle WA) Ultralite T-700'" (Ultra Diagnostics Corp, Seattle WA) Carboxycyanine derivatives (for example, cyanine 5.18 from Molecular Probes or Jackson Immunoresearch Labs, Inc. of West Grove, PA) Nuclear Stains Chromomycin A3 (Sigma Chemical co.)(DNA specific and spectrally similar to fluorescein) Ethidium bromide Propidium iodide -. LD700 (from Exciton Chemical Co., Dayton, OH) Acridine Orange Pararosaniline (end product of Feulgen reaction) Physioloaical Indicators Fluo-3n (calcium indicators) (Molecular Probes Inc.) Rhod-2" (calcium indicators) SNAFU" (ph indicators) '.' 35 SNARF'" (ph indicators) -While the present invention has been described in connection with the preferred embodiment thereof, it will be understood that many modifications will be readily apparent ';'.;' 40 to those of ordinary skill in the art, and this application is intended to cover any adaptations or variations thereof.
The present invention is intended to be used in many fields - of art analogous to, and in addition to the fields described above, including flow cytometry. Therefore, it is manifestly 45 intended that this invention be limited only by the claims and equivalents thereof.
~~ 206188 Field of the Invention The present invention relates to confocal microscopy and in particular to laser scanning confocal microscopy in which laser light is used to excite dyes in a specimen.
Background of the Invention Confocal microscopy is well known in the art.
The concept of confocal microscopy is that the image viewed by the microscope is confined to a very precise ' .. focal plane by limiting the depth of field of the image.
Only those portions of the specimen which are in focus are detected. Out of focus regions of the sample appear dark. By changing the position of the focal plane, this important principle defines one major method for achieving optical sectioning.
The earliest versions of confocal microscopes used direct vision design with incoherent illumination.
The field of illumination in the specimen was limited by a pin hole positioned on the illumination axis. The image of this pin hole is then projected on the specimen by a condenser lens. The illuminated point on the specimEn reflects light (or as described below, emits fluorescent light). The reflected light of the image is then focused through an objective lens onto a detector.
Either the specimen or the light focused on the image is scanned in a raster pattern so that the detector collects pixel information from a region of the specimen. The pixel information is then passed through a computer which a .:
can generate an image of the overall specimen.
iY'.'.
r:', _ The concept of the scanning confocal microscope is described in US Patent 3,013,467 to Marvin Minsky, which is hereby incorporated by reference. The optical path of the scanning confocal microscope may be constructed in trans-illuminating mode in which a =:.~, separate condenser and objective lens is used in the same y. axis. In the alternative, the optical path of the ,,, ' WO
v, P~ w 6~~~~ -2- .
, , '.J '..
scanning confocal microscope may be constructed in an epi-illuminating mode making a single objective lens , serve both as the condenser and objective lens and using a dichroic or half mirror to collect the emitted light , . 5 into a detector, as shown in Figure 1.
In the Minsky patent, the raster scan is generated by moving the stage on which the specimen is supported by two orthogonally vibrating tuning forks that w are driven by electromagnets. As the stage is moved in a .
raster scan pattern, the resulting image detected by the ., image detector is a serial raster scanned image.
. The use of fluorescent dyes to stain the specimen being viewed further improved the range of applications to which scanning confocal microscopy could be applied. Especially in the area of immunofluorescence histochemistry and in other neuroanatomical techniques, ., the staining of specimens with dyes is particularly useful to aid in distinguishing different features within biological tissues. The stains may comprise dyes designed only to absorb light or dyes that emit light in response to absorption, which is called fluorescence.
Fluorescent dyes have the advantage over dyes which only absorb light in that a given fluorescent marker will be visible only when illuminated with the appropriate filter set.
Fluorescence is a consequence of the .,, interaction of a photon with a fluorophore. When a '' .y photon of light is absorbed by a molecule it may increase the potential energy of the molecule by raising an electron to a higher orbital state. An electron raised to a higher orbital state from its natural state will 'v' tend to revert to the natural state. When the electron a.- :.
falls from a higher to a lower orbital state, energy is .. released which is equal to the difference in energy .. 35 between the two orbital states. When this occurs, part or all of its energy may be released as a photon having a <.~;,~ .
o.~i;; . . . .
-3- . v206,"~188 j . wavelength (spectral line) proportional to the released energy. The resulting luminescence is called fluorescence (and in some circumstances phosphorescence).
Excitation of a fluorophore molecule at one wavelength typically results in fluorescent emission at longer . wavelengths of light.
The scanning laser confocal microscope improved y on the design of the scanning confocal microscope and the use of fluorophores by using coherent light to scan the stained specimen. The monochromaticity, high intensity and lack of divergence of the laser light contributed to improvements in the resulting images. In an epi-illuminating laser scanning confocal microscope of the ' prior art, as shown in Figure 2, the laser light 200 is scanned onto the specimen 220 from above and is reflected to a detector 215 in the same focal path as the incident light through the use of a half mirror or dichroic mirror 205. Typically, the specimen is stained with fluorescent dyes to enhance specific features within the specimen which may be of interest.
The MRC-600 laser scanning confocal imaging system, shown diagrammatically in Figure 2, is manufactured by BioRad Microscience of Hemel Hempstead, Herts, England. This laser scanning confocal microscope system is adaptable for use with a number of upright and inverted microscopes available from microscope vendors such as Nikon, Zeiss, Olympus and Leitz. The coherent illumination is an argon ion laser 201 having primary lines at 514 and 488 manometers (nm). The emitted laser light 200 also has a plurality of minor spectral lines as determined by argon. The lines are filtered by the external filter 203 which selects either the 488nm (blue) line the 514nm (green) line by means of an excitation filter 203. The selected light is reflected by a beam splitter 205 which includes a dichroic mirror used for fluorescent imaging. If simple reflection imaging is ~' ~ :~ ~ ~~
.. . Q ~' _4_ required, a semi-reflecting or half mirror may be used in place of the dichroic mirror 205.
The argon ion laser is available from Ion Laser Technology Company of Salt Lake City, Utah, part number , 5425A. The argon ion laser is used to excite yluorescent dyes in the specimen which emit light slightly shifted in the spectrum in response to the excitation wavelength of the spectral lines of the laser light. The dyes are selected based upon their sensitivity to light, their ", 10 affinity for features desired to be viewed in specimens and their fluorescent capabilities.
The light 200 from the laser is passed through the scanning unit 207 where it is raster scanned in an XX
scanning movement by means of two oscillating mirrors.
The laser beam is then passed through a microscope eyepiece onto the specimen such that a scanning spot caused by the scanning unit 207 scans the specimen.
Reflected light or fluorescent light from the specimen passes back through the scanning system along the same path as the incident laser light. Reflection of the light is so rapid that the mirrors have not shifted ' position so that the light retraces the exact original path in the reverse direction. A portion of the reflected or fluorescent light.passes through a half ..::
mirror or dichroic mirror 205 to be passed to photomultiplier tubes.
The laser scanning confocal imaging system from BioRad shown in Figure 2 attempts simultaneous imaging of two different fluorescent stains. The 514nm spectral line from argon ion laser 201 is used to excite both fluorescein isothiocyanate (fluorescein) and Texas Red"
(from Molecular Probes, Inc.) conjugated probes. This attempts the simultaneous excitation of different fluorescent dyes to allow selected features of the specimen to be stained in different colors and viewed together. The dual images are picked up by ~;.,.
-5- ~ 2067188 photomultiplier tubes 213 and 215. A second beam splitter 207 is a dichroic mirror allowing light of one wavelength to be directed to photomultiplier tube 213 while light having other wavelengths passed to photomultipiiar 215.
w' The two images received from photomuitiplier tubes 213 and 215 are used by a computer 222 to construct an image on display 224 of the specimen in a single focal plane. The simultaneous imaging of two different fluorescent stains at exactly the same focal plane would ';, allow the identification of different specific features in the same specimen. A shortcoming of the dual color laser scanning confocal microscope system of the prior art is that the 514nm line of the argon ion laser produces simultaneous excitation of the two fluorescent dyes (fluorescein and Texas Red~). This simultaneous excitation causes false imaging and the loss of feature ,, detail in the resulting image generated by the computer.
Figure 3 shows a graph published by BioRad Microscience indicating the absorption and emission >.:~> ' spectra of fluorescein and Texas Red'. The graph is reproduced from BioRad and only approximates the spectrums. Curve 301 describes the absorption spectra of fluorescein while curve 303 shows the emission spectra of fluorescein. Curve 305 shows the absorption spectra of Texas Red'M and curve 307 describes the emission spectra of Texas Red''. As can be seen in Figure 3, there is an ., area of overlap between the absorption spectrums of Texas Red"~ and fluorescein at 514nm. Thus, simultaneous excitation and emission of fluorescein and Texas Red'' occurs when excited with the single 514nm line of the argon laser. Also shown in Figure 3 is a large area of overlap between the emission spectra of Texas Red'T' and the emission spectra of fluorescein.
The response curves for the filters and the dichroic reflectors are placed below the absorption and ~~'~$$ - 6 - .;,,~, emission spectra of fluorescein and Texas Red'T' in Figure 3 for comparison. .i~hen using an argon laser to excite , the dyes, the 514nm line of the dye is the only line allowed to pass through the exciter filter 203 shown in Figure 2. The narrow wavelength response curve 309 of Figure 3 is for the exciter filter 203. The response curve 311 is for dichroic reflector 205 and the response curve 313 is for dichroic reflector 207. The response curve 315 is for green channel filter 211 and the IO response curve 317 is for red channel filter 209.
As can be seen in Figures 3, the intent is to have the single 514nm line of the argon laser excite both w the fluorescein and Texas Red"' dyes. The emission spectra of these respective dyes are then selected to be passed to photomultiplier tubes 213 arid 215 shown in Figure 2 to be independently detected for reconstructing a two color image at the same focal plane. The problem .17 with this prior art technique is that the single excitation line from the argon laser excites fluorescein ~?, 20 much more efficiently than Texas Red. For example, as w;.,,shown in Figure 3, the excitation of the fluorescein dye at a wavelength of 514nm is at approximately 50%. The excitation of Texas Red"" at the same 514nm wavelength, ., however, is very low (less than 3%). Since the emission spectra of the dyes corresponds to, and is proportional to the amount of energy absorbed by the dyes, the low amount of absorbed energy from the 514nm line by Texas Red'1° will result in a very low amount of emitted .; fluorescent light. Hence, the amount of fluorescein emission seen in the red channel can vary according to the relative concentrations of fluorescein and Texas Red's. Unless the relative concentrations and saturation of the dyes accurately controlled, the emission spectra of Texas Red's may be swamped by the "spillover" of the longer wavelengths of the fluorescein emission spectra.
This confusion will result in images in which many of the x«°:3, _7_ ~ 206y.~88 features stained only with fluorescein will appear in both images. One solution to this problem is to use separate laser lines to better excite both fluorescent dyes.
Multiple line excitation of specimens dyed with different fluorochromes using two lasers is also known in the prior art. For example, a Spectra-Physics 2025 argon ' ion 3-watt water cooled laser (tunable to a single argon ion line between 351nm through 528nm) has been confocally aligned with a 5 milliwatt air-cooled argon ion laser having fixed wavelengths at 488nm and 514nm. The alignment of two lasers, however, presents extreme focusing problems. The two light paths must be aligned to exacting standards to ensure that the same focal plane is observed.
Summary of the Invention The shortcomings of the prior art described . above and other shortcomings of the prior art which will be recognized and understood by those skilled in the art upon reading and understanding the present specification are overcome by the present invention. The present invention teaches a true multi-color laser scanning confocal imaging system for use-with a microscope in which a single laser having a multi-line output is used to simultaneously or individually excite a plurality of dyes. The images may be simultaneously viewed by a plurality of photomultiplier tubes to reconstruct an image showing distinct features of a specimen stained with different dyes. The images may also be constructed using a single detector in a time-multiplex fashion and using a computer to construct the image.
:,.~~~ ;
~~~,,:.. -8-., Description of the Drawinas In the drawings where like numerals refer to .
bike components throughout the several views, Figure l~is a diagram showing a prior art optical confocal microscope system.
Figure.2 is ~a diagram showing a prior art laser , '. scanning confocal imaging system.
Figure 3 shows the response spectra of the' . various components of Figure 2.
Figure 4 shows a typical layout of the various ;y components for the present invention. w ''~' Figure 5 is a diagram showing a two-color optical confocal microscope system using two detectors.
Figure 5a shows the response spectra of the ' 15 various components of Figure 5.
V'''''' Figure 6 is a diagram showing a time-multiplex single detector laser scanning confocal imaging system.
Figure 7 shows the absorption and emission spectra of various fluorochromes.
Figure 8 shows the response spectra of the various filters and dichroic reflectors used in the time-multiplex single detector laser scanning confocal imaging system of Figure 6.
Figure 9 is a diagram showing a multi-detector, multicolor optical confocal microscope system using three detectors.
Detailed Description of the Preferred Embodiment In the following detailed description of the preferred embodiments, references made to the accompanying drawings which form a part hereof and in which is shown by way of illustration specific embodiments in which the invention may be practiced.
These embodiments are described in sufficient detail to enable those skilled in the art to practice the invention, and it is to be understood that other ~
_9_ ~os~y g~~=:
embodiments may be utilized and that structural or physical changes may be made without departing from the spirit and the scope of the present invention. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope of the present invention is defined by the appended claims.
Figure 4 shows a typical layout of the various components for the present invention. The layout is similar to that of the MRC-600 laser scanning confocal -imaging system manufactured by BioRad Microscience Ltd.
of Hemel Hempstead, Herts, England. The present laser scanning confocal microscope system is also adaptable for ."~'r' use with a number of upright and inverted microscopes available from microscope vendors such as Nikon, Zeiss, . 15 Olympus and Leitz. The main optics and scanner head of the present invention are housed cabinet 401. The source of laser light 403 is supported near the cabinet so that the mufti-line laser light enters the cabinet. In the configuration shown, the incident laser light exits the cabinet to enter the microscope 405 from the top. The reflected of emitted light is received from the microscope along the same optical path as the incident laser light.
Cabinet 401 also contains the detectors, which in the preferred embodiments are photomultiplier tubes.
Those skilled in the art will readily recognize that other detectors may be used such as CCD devices, vidicon tubes, etc. The detectors within the cabinet and the scanners are connected to computer 407 which constructs the images of the specimen and displays them on display 409.
Figure 5 is a schematic diagram of a basic two-color imaging system of a preferred embodiment of the invention. The scanning unit and other mirrors (described more fully below) of the scanning confocal microscope shown in Figure 5 have been omitted for ~ PCT/US91/00607 ~,o . -lo-clarity. Figure 5a is a series of graph depicting the ,,; spectral response curves for the components of Figure 5.
Figures 5 andw5a should be viewed together. The laser .. light source 501 is an air-cooled krypton/argon ion laser, Model No: 5470-KBR, available from Ion Laser ':. Technology in Salt Lake City, Utah. This laser produces dominant spectral lines at 488nm, 568nm, and 647nm. The design of this laser suppresses other minor lines to ensure the emission of only the 488nm, 568nm, and 647nm .
lines. As will be described more fully below, other lasers may be used and other selected lines of laser light may be used to implement the preferred embodiments of the present invention without departing from the spirit and the scope of the claims.
The laser light 500 is filtered through excitation filter block 503. Excitation filter block 503 . contains a plurality of filters selectable by the user.
The filter shown selected is 503a, which is a dual bandpass filter allowing the passage of light at both 488nm and 568nm. Response curves 553a and 553b of Figure 5 describe the spectral response of dual band filter 503a. The selection of two lines from laser 501 allows for the excitation of two dyes in the specimen. Response curves 551 and 552 of Figure 5a correspond to filters 503b and 503c, respectively. Filters 503b and 503c may be used to individually select the 488nm or 568nm lines, respectively, from laser 501.
The filtered laser light is then passed to a dual dichroic filter block 505. The dual dichroic filter block is selected to reflect both the 488nm and the 568 nm lines. It is also selected to transmit from 500-540 nm for the fluorescent light emitted from fluorescein, and 585-650nm for the fluorescent light emitted from ' Texas Red'. Response curve 555 of Figure 5 depicts the spectral response of dichroic mirror 505.
CVO 92/02839 PC'T/US91/00607 ~:~.a ' , ;.;
..
The excitation of fluorescein causes the dye to emit light at a shifted wavelength with a longer wavelength than the excitation light. The incident laser light with lines at 488nm and 568nm is directed onto the specimen 507. The specimen has been stained with . fluorescein and Texas Red~ conjugated probes to highlight features of the specimen. The emitted light from the .' dyes follows the same path as the excitation laser light and strikes dual dichroic filter block 505. As described above, this filter block 505 has been selected to pass light in the wavelength of 500-540nm for fluorescein, and 585-650nm for Texas Red"". Response curve 555 of Figure 5 shows the dual bandpass spectral response of dichroic mirror 505.
The emitted light strikes several reflectors shown generally as reflect~.~r 509, which directs the light to a second filter block 511. Filter block 511 includes a second dichroic mirror 521, which passes light in the 585nm-650nm range and reflects light in the 500nm-540nm range. Response curve 561 of Figure 5 shows the spectral response of dichroic mirror 521. Photomultiplier tube 513 receives and detects emitted light passed from dichroic mirror 511 and filtered through low pass filter 515. Filter 515 is, in the preferred embodiment, a 585 LP long pass filter available from Omega. Response curve 562 of Figure 5 shows the spectral response of filter 517. Photomultiplier tube 513 is connected to a computer (not shown in this diagram) where the information is used to construct an image in the selected focal plane on the specimen 507. The scanning head is also not shown in Figure 5 for brevity of discussion.
Light reflected from filter block 511 in the 500-540 nanometer range is passed through filter 517, which in the preferred embodiment is a bandpass filter 522 DF 35 available from Omega. Response curve 563 of Figure 5 shows the spectral response of filter 515.
The CVO 92/02839 ~ PCT/US91 /00607 6'1~.$ .
passed light is detected by photomultiplier tube 519.
The detected information is then sent to the same computer connectedvto photomultiplier tube 513, where a second image representative of the features stained with fluorescain in specimen 507 is created by the computer.
The image detected by photomultiplier tube 513 represents features stained with the dye Texas Red'. The images formed by the computer detected by the two photomultiplier tubes are in the exact focal plane, since the same laser light beam is used to scan the same focal plane of the specimen without moving any parts. Thus, a true multi-color simultaneous imaging system is constructed where dyes are individually excited by different lines from the same laser.
Excitation filter block 503 contains band pass .. filters 503b and 503c for individual selection and viewing of stained areas corresponding to fluorescein and Texas Red'. Since the filter blocks containing the dichroic mirrors are not moved when switching excitation filters, the resulting images are perfectly aligned with respect to the focal plane. Thus, the user can select single color or a perfectly aligned multi-color image to be constructed by the computer.
Those skilled in the art will readily recognize that the excitation of dyes by the krypton/argon laser 501 is facilitated by the selection of the spectral lines of the laser light. Those skilled in the art will readily recognize that a krypton laser having dominant lines at 476/482nm, 520nm, 568nm and/or 647nm may be used to excite selected dyes and obtain results similar to those described above in conjunction with Figure 5.
Thus, a krypton laser with minor adjustments made to the filters and dichroic mirrors will produce acceptable ._ results useable with the present invention.
Figure 6 shows a multi-color, single-detector scanning laser confocal imaging system of an alternate WO 92102839 PCf/US91/00607 t ~.: ~:.
-13- , , ,~ e~:
J
preferred embodiment of the present invention. The multi-color images are serially constructed from a single detector by time-multiplex gathering of information by the computer. The laser selected for use in this embodiment is also an air-cooled krypton/argon ion laser, Model 5470-KBR available from ILT. Those skilled in the ', art will readily recognize that, by appropriate selection of filters and dichroic mirrors, other lasers, such as a krypton laser could be used with the present invention as described in conjunction with Figure 6, such as an air-cooled krypton laser, Model 5470K available from Ion Laser Technology. Other vendors produce lasers which would be acceptable with the present invention.
Krypton/argon ion laser 601 produces dominant spectral lines at 488nm, 568nm, and 647nm. Table 1 ",: describes the selection of filters and mirrors to be used with the krypton/argon laser. In the construction of the preferred embodiment of the present invention described in conjunction with Figure 6, the excitation filter 607, the dichroic mirror 609 and the emission filter 611 are all mounted together in a single filter block 605.
In this fashion, matched sets of these filters may be easily substituted without disturbing the other optics by merely r eplacing the filter blocks 605.
Filter Laser Excitation Dichroic Emission Block Line Filter Mirror Filter Blue 488 nm 488 DF 10 500 DCLP 522 DF 35 Yellow 568 nm 568 DF 10 585 DCLP 600 DF 20 Red 647 nm 647 DF 10 660 DCLP 665 LP
The krypton gas of the laser produces spectral lines . at 476/482nm, 520nm, 568nm and 647nm, among others. The argon gas produces spectral lines at 488nm and 514nm, among 'i a .. s others. The krypton/argon laser is designed to suppress all lines except those at 488nm, 568nm and 647nm. Since the 488nm line from. the argon gas excites fluorescein more efficiently,~the mixed gas krypton/argon laser is preferred.
Those skilled in the art will readily recognize, however, that adequate power from the 476/482nm line of a krypton can excite fluorescein for use in the present invention. Hence, a krypton laser may be substituted for use with the present invention with the appropriate matching filters and dichroic mirrors.
The preferred krypton/argon laser from ILT is air-cooled since it is inexpensive and easily cooled. Since liquid or water-cooled lasers suffer much vibration due to the pumping of the liquid around the tube for coolant, air-cooled lasers are preferred. Air-cooled lasers, of course, are also preferred because of the cost differential between air-cooled and water-cooled high-powered lasers.
Referring once again to Figure 6, the specimen 603 is dyed with three dyes: fluorescein, Lissamine rhodamine (or Texas Red'"'), and cyanine 5.18. These dyes can be excited by the laser lines described for the krypton/argon laser and be detected by the photomultiplier tube without interference from the other dyes. In some cases, however, higher light levels for the cyanine 5.18 dye may be required due to the lower sensitivity of the photomultiplier tube to red light.
Figure 7 should be viewed in conjunction with an explanation of laser 601 of Figure 6. Figure 7 shows a graph of the absorption spectra and emission spectra of selected ., dyes which may be used to stain specimen 603 of Figure 6.
.. . , The graph of Figure 7 shows the spectra curves normalized on a scale of zero to one hundred as a measure of relative -intensity to one another. Curve 701 corresponds to the absorption spectra of fluorescein and curve 703 corresponds to the emission spectra of fluorescein. Curve 705 corresponds to the absorption spectra of Lissamine rhodamine and curve 709 corresponds to the emission spectra of WO 92/02839 ; PCT/US91/00607 ".
-15- ~ 20671188 Lissamine rhodamine. Curve 711 corresponds to the absorption spectra of cyanine 5.18 and curve 713 corresponds to the emission spectra of cyanine 5.18. tdith proper selection of .. , excitation light, the emission and absorption spectra of the various selected dyes are sufficiently removed to allow filtering and detection by separate photo multiplier tubes as v shown in Figure 6.
Figure 8 is a description of the response of the various filters of Figure 6. The response curves are described as being part of one of three filter blocks: blue, yellow and red. Response curve 801 corresponds to the response curve of a 488 emission filter Part No. 488 DF10 available from Omega Instruments, Inc. Curve 803 is the dichroic mirror 500 DCLP long pass filter available from Omega. Response curve 805 corresponds to emission filter 522 DF 35 available from Omega. Response curves 801, 803 and 805 are part of the blue filter block.
For the yellow filter block, response curve 807 corresponds to the 10 nanometers wide emission filter Part No. 568 DF 10. Curve 809 corresponds to dichroic mirror ,., Part Nc. 585 DCLP available from Omega. Curve 811 :w5.; .
corresponds to the emission filter Part No. 600 DF 20 also available from Omega.
The red filter set corresponds to curves 813, 815 and 817. Curve 813 is the response curve for the excitation filter Part No. 647 DF 10. Curve 815 corresponds to the long pass dichroic mirror filter 660 DCLP available from Omega.
Curve 817 corresponds to the emission filter which is a long pass filter 665 LP also available from Omega.
Referring once again to Figure 6, a time-multiplexed, three-colored confocal microscope is implemented by changing the filter blocks 605 corresponding to the colors desired to be viewed in the specimen 603. The filter block 605 comprised of excitation filter 607, the dichroic mirror 609 and the emission filter 609 are all changed together to w'. correspond to the specific dye being viewed. The multi-WO 92/02839 ~~ PCT/US91/00607 ~~~~; i: i . . _ -16-spectral line laser light 600 from laser 601 enters the . selected excitation filter 607 which narrowly selects one of , the available laser lines from the krypton/argon laser. The laser light with the selected line is reflected by preselected dichroic mirror 609 which corresponds to the selected line.
Dichroic mirror 609 will reflect the laser light containing the selected line onto the XY scanning unit 613 which causes the laser beam to be raster scanned on the specimen. XY scanning unit 613 is available within the BioRad Microscience MRC-600 confocal imaging system. The scanning unit 613 contains two mirrors which are connected to galvanometers which move the mirrors at selected scanning . , rates. One of the mirrors is responsible for generating an X
axis scan while the other mirror produces a Y axis scan. The scanning is synchronized to the receipt of images by the photomultiplier tubes and the generation of computer images ,, by means of a scan card and frame store in the computer 620.
The scanned laser light containing the laser line of interest is projected through the microscope objective onto specimen 603. The dye corresponding to the selected laser line fluoresces and emits a longer wavelength light in response to the excitation. The longer wavelength emitted light is passed back along the same optical path through scanning unit 613 to dichroic mirror 609. The longer wavelength emitted light passes through dichroic mirror 609 to emission filter 611. The emission filter is selected from the group described above~corresponding to the selected laser y:~; 30 line and dye to be viewed.
The emitted light through filter 611 is passed to the photomultiplier tube 615 where the scanned image is received, converted to electrical images and passed to the computer 620. The computer 620 reconstructs the image for ., . 35 the particular dye being excited by the selected line.
:~!7 ,r J hJ
-17- ~ 20fi'~~.88 This process is duplicated for each of the colors desired to be viewed. The filter block 605 containing filters 607, 611 and dichroic mirror 609 can be easily changed without disturbing the alignment of the laser, the specimen or the photomultiplier tube. The specimen can then be scanned with the filter block for the second dye.
However, by changing filter blocks, the region on the focal plane scanned may shift slightly in the XY plane due to the small differences in the angle of the dichroic mirrors in the .
filter blocks. After acquiring the images, the computer can combine and align the two images to produce a true two-color or pseudo color image. Quite often a pseudo color image is created wherein one color on the computer generated image . corresponds to a detected color from the specimen. The color detected from the specimen may not correspond to the color used by the computer to highlight the features stained by that particular dye since it may be more aesthetically pleasing to view higher contrasting colors than the actual colors received from the specimen.
.
In addition, the filter block 620 may be replaced by the third filter set and a third color scanned and combined with the previous two images to generate a true three-colored ,. image by computer 615.
Figure 9 shows a true three-color laser scanning confocal microscope which does not require the substitution of filter blocks to generate a three-color image. With the embodiment shown in Figure 9, a simultaneous three-color image may be scanned in which all three laser lines excite the dyes simultaneously. Laser 601 is a krypton/argon laser E, as described above. The multi-line laser light 600 passes through a broad-bandpass filter 907 where it is reflected by multi-passband dichroic mirror 909. The laser excitation light 600 is raster scanned by scanning unit 913 and enters the microscope eyepiece.
The specimen 603 is stained with dyes as described above which fluoresce when excited. The emitted light follows the WO 92/02839 ~~~ PGT/US91/00607 . , . ., ,; y , , . -18 - . ,.
same optical path followed by the excitation J.aser light through the scanning unit 913. The emitted light has a longer wavelength than the excitation light and passes through multi-passband dichroic mirror 909. The emitted light then strikes a second dichroic mirror 917 selected to ;,; reflect blue light and pass the other colors.
Photomultiplier tube 915 receives blue light emitted by fluorescein as filtered by emission filter 607.
The longer wavelength emitted light has passes through the second dichroic mirror 917 where it strikes a third dichroic mirror 919 selected to reflect red light and pass longer wavelength red light. Photomultiplier tube 921 receives red light emitted by Lissamine rhodamine (or Texas Red"~~ as filtered by emission filter 925. Photomultiplier tube 923 receives longer wavelength red light emitted by cyanine 5.18.
Fluorescein conjugated probes are one of several dyes available for use in conjunction with the preferred embodiments of the present invention in staining specimens .: ..
and examining selected features. Table 2 describes a number of dyes that may be used with the present invention.
i.: .::
~
.:
-19- ~ ~ ..:~. p.6'~ 18 8 Fluorescent Dyes for Con~uaation Fluorescein isothiocyanate ~FITC) Borate-dipyrromethane ("Bodipy) Lucifer Yellow Tetramethylrhodamine isothiocyanate (TRITC) Lissamine rhodamine Texas Red'" (from Molecular Probes, Inc.) Allophycocyanine Ultralite T-680"' (Ultra Diagnostics Corp, Seattle WA) Ultralite T-700'" (Ultra Diagnostics Corp, Seattle WA) Carboxycyanine derivatives (for example, cyanine 5.18 from Molecular Probes or Jackson Immunoresearch Labs, Inc. of West Grove, PA) Nuclear Stains Chromomycin A3 (Sigma Chemical co.)(DNA specific and spectrally similar to fluorescein) Ethidium bromide Propidium iodide -. LD700 (from Exciton Chemical Co., Dayton, OH) Acridine Orange Pararosaniline (end product of Feulgen reaction) Physioloaical Indicators Fluo-3n (calcium indicators) (Molecular Probes Inc.) Rhod-2" (calcium indicators) SNAFU" (ph indicators) '.' 35 SNARF'" (ph indicators) -While the present invention has been described in connection with the preferred embodiment thereof, it will be understood that many modifications will be readily apparent ';'.;' 40 to those of ordinary skill in the art, and this application is intended to cover any adaptations or variations thereof.
The present invention is intended to be used in many fields - of art analogous to, and in addition to the fields described above, including flow cytometry. Therefore, it is manifestly 45 intended that this invention be limited only by the claims and equivalents thereof.
Claims (16)
1. A multi-color confocal microscopy system for use with an optical microscope in viewing a specimen stained with a plurality of stains, which stains fluoresce when excited by light of particular frequencies, comprising:
laser means for producing multi-line incident laser light having multiple excitation lines from a single laser light source, each of said excitation lines corresponding to an excitation frequency of one of the stains;
means for directing said incident laser light into the microscope and for receiving emitted light from the microscope, said emitted light having multiple fluorescent emissions, each of said fluorescent emissions corresponding to an excitation frequency of one of the stains;
detector means positioned to receive said emitted light for converting said emitted light into electrical signals; and control means connected to said detector means for accumulating said electrical signals and for producing a plurality of images of the specimen at a precise focal plane, each of said images corresponding to one of said lines of said laser.
laser means for producing multi-line incident laser light having multiple excitation lines from a single laser light source, each of said excitation lines corresponding to an excitation frequency of one of the stains;
means for directing said incident laser light into the microscope and for receiving emitted light from the microscope, said emitted light having multiple fluorescent emissions, each of said fluorescent emissions corresponding to an excitation frequency of one of the stains;
detector means positioned to receive said emitted light for converting said emitted light into electrical signals; and control means connected to said detector means for accumulating said electrical signals and for producing a plurality of images of the specimen at a precise focal plane, each of said images corresponding to one of said lines of said laser.
2. The multi-color confocal microscopy system according to claim 1 further including means connected to said laser means for suppressing the production of excitation lines which would excite more than one stain.
3. The multi-color confocal microscopy system according to claim 1 further including filter means positioned in the path of said incident laser light for selectively passing a selected one of said excitation lines from said laser means.
4. The multi-color confocal microscopy system according to claim 1 further including filter means positioned in the path of said emitted light for selectively passing a selected emission of said fluorescent to said detector means.
5. The multi-color confocal microscopy system according to claim 4 wherein said filter means includes dichroic mirrors positioned in the path of said emitted light for separating each of said fluorescent emissions of into separate line-paths and for directing each of said line-paths into one of a plurality of detectors.
6. The multi-color confocal microscopy system according to claim 3 wherein said detector means includes means for detecting one line at a time and forming a multi-color optical image on a time-multiplexed basis.
7. The multi-color confocal microscopy system according to claim 1 wherein said means for directing further includes means for scanning said incident laser light onto the specimen in a raster-scan format and wherein said detector means further includes means for descanning said reflected light.
8. The multi-color confocal microscopy system according to claim 1 wherein said control means further includes a computer having a display means for displaying the specimen in a plurality of pseudo-colors, each of said pseudo-colors corresponding to the fluorescent emission of the emitted light of one of the stains.
9. The multi-color confocal microscopy system according to claim 1 wherein said laser means further includes a single krypton-argon laser.
10. The multi-color confocal microscopy system according to claim 9 wherein said krypton-argon laser is configured to produce a plurality of laser lines such that each line excites at most only one of Fluorescein, Lissamine Rhodamine, and cyanine 5.18 stains.
11. The multi-color confocal microscopy system according to claim 1 wherein said detector means further includes photomultiplier tubes.
12. A multi-color confocal microscopy system for use with an optical microscope viewing a specimen stained with a plurality of stains, comprising:
a multi-line laser producing laser light having a plurality of lines, some of said lines being selectively prevented from exiting said laser, and some other of said lines being selectively allowed to exit said laser as excitation lines, each of said excitation lines selected to corresponding to an excitation frequency of only one of the plurality of stains;
a plurality of excitation filters each selectively placed in the path of said laser light;
a first dichroic mirror placed in the path of said laser light behind said excitation filters, said first dichroic mirror selected to reflect excitation lines and to pass emitted fluorescent light;
a scanning unit placed to receive said laser light from said first dichroic filter and reflect said laser light in a raster-scanned form into the optical microscope;
said scanning unit further placed to receive said emitted fluorescent light from the optical microscope, to descan said raster-scanned form and to reflect said emitted fluorescent light back through said first dichroic filter;
a second dichroic mirror placed in the path of said fluorescent light behind said first dichroic filter, said first second mirror selected to reflect some wavelengths of said fluorescent emission of said emitted light and pass other wavelengths of said emitted fluorescent light;
and a first detector placed to receive said reflected florescent light passed from said second dichroic mirror and a second detector placed to receive said reflected florescent light reflected from said second dichroic mirror.
a multi-line laser producing laser light having a plurality of lines, some of said lines being selectively prevented from exiting said laser, and some other of said lines being selectively allowed to exit said laser as excitation lines, each of said excitation lines selected to corresponding to an excitation frequency of only one of the plurality of stains;
a plurality of excitation filters each selectively placed in the path of said laser light;
a first dichroic mirror placed in the path of said laser light behind said excitation filters, said first dichroic mirror selected to reflect excitation lines and to pass emitted fluorescent light;
a scanning unit placed to receive said laser light from said first dichroic filter and reflect said laser light in a raster-scanned form into the optical microscope;
said scanning unit further placed to receive said emitted fluorescent light from the optical microscope, to descan said raster-scanned form and to reflect said emitted fluorescent light back through said first dichroic filter;
a second dichroic mirror placed in the path of said fluorescent light behind said first dichroic filter, said first second mirror selected to reflect some wavelengths of said fluorescent emission of said emitted light and pass other wavelengths of said emitted fluorescent light;
and a first detector placed to receive said reflected florescent light passed from said second dichroic mirror and a second detector placed to receive said reflected florescent light reflected from said second dichroic mirror.
13. A method of viewing a specimen stained with a plurality of stains, which stains fluoresce when excited by light of particular frequencies, comprising the steps of:
producing multi-line incident laser light having multiple excitation lines from a single laser light source, each of said excitation lines corresponding to an excitation frequency of one of the stains;
directing said incident laser light into a microscope holding the specimen;
receiving emitted light from the microscope, said emitted light having multiple fluorescent emissions, each of said fluorescent emissions corresponding to an excitation frequency of one of the stains;
detecting said emitted light and converting said emitted light into electrical signals; and accumulating said electrical signals and producing a plurality of images of the specimen at a precise focal plane, each of said images corresponding to one of said lines of said laser.
producing multi-line incident laser light having multiple excitation lines from a single laser light source, each of said excitation lines corresponding to an excitation frequency of one of the stains;
directing said incident laser light into a microscope holding the specimen;
receiving emitted light from the microscope, said emitted light having multiple fluorescent emissions, each of said fluorescent emissions corresponding to an excitation frequency of one of the stains;
detecting said emitted light and converting said emitted light into electrical signals; and accumulating said electrical signals and producing a plurality of images of the specimen at a precise focal plane, each of said images corresponding to one of said lines of said laser.
14. The method according to claim 13 further including the step of suppressing the production of excitation lines which would excite more than one stain.
15. The method according to claim 13 further including the steps of filtering said incident laser light and selectively passing a selected one of said excitation lines.
16. The method according to claim 13 further including the steps of filtering said emitted light and for selectively passing a selected emission of said fluorescent.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/565,625 US5127730A (en) | 1990-08-10 | 1990-08-10 | Multi-color laser scanning confocal imaging system |
| US07/565,625 | 1990-08-10 | ||
| PCT/US1991/000607 WO1992002839A1 (en) | 1990-08-10 | 1991-01-28 | Laser for confocal microscope |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2067188A1 CA2067188A1 (en) | 1992-02-11 |
| CA2067188C true CA2067188C (en) | 2001-05-15 |
Family
ID=24259447
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002067188A Expired - Lifetime CA2067188C (en) | 1990-08-10 | 1991-01-28 | Multi-color laser scanning confocal imaging system |
Country Status (9)
| Country | Link |
|---|---|
| US (1) | US5127730A (en) |
| EP (1) | EP0495930B1 (en) |
| JP (1) | JP2824462B2 (en) |
| AT (1) | ATE179527T1 (en) |
| CA (1) | CA2067188C (en) |
| DE (2) | DE69131176T2 (en) |
| DK (1) | DK0495930T3 (en) |
| ES (1) | ES2133283T3 (en) |
| WO (1) | WO1992002839A1 (en) |
Families Citing this family (236)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB9015793D0 (en) * | 1990-07-18 | 1990-09-05 | Medical Res Council | Confocal scanning optical microscope |
| US5214658A (en) * | 1990-07-27 | 1993-05-25 | Ion Laser Technology | Mixed gas ion laser |
| US5296703A (en) * | 1992-04-01 | 1994-03-22 | The Regents Of The University Of California | Scanning confocal microscope using fluorescence detection |
| DE4323129C2 (en) * | 1992-07-24 | 2002-10-02 | Zeiss Carl | Inverted microscope |
| GB9302799D0 (en) * | 1993-02-12 | 1993-03-31 | Medical Res Council | Detecting means for a scanning optical microscope |
| US5547849A (en) * | 1993-02-17 | 1996-08-20 | Biometric Imaging, Inc. | Apparatus and method for volumetric capillary cytometry |
| US5280548A (en) * | 1993-03-11 | 1994-01-18 | Boc Health Care, Inc. | Emission based fiber optic sensors for pH and carbon dioxide analysis |
| US5923430A (en) | 1993-06-17 | 1999-07-13 | Ultrapointe Corporation | Method for characterizing defects on semiconductor wafers |
| USH1530H (en) * | 1993-06-17 | 1996-05-07 | Ultrapointe Corporation | Surface extraction from a three-dimensional data set |
| US5479252A (en) * | 1993-06-17 | 1995-12-26 | Ultrapointe Corporation | Laser imaging system for inspection and analysis of sub-micron particles |
| US5463897A (en) * | 1993-08-17 | 1995-11-07 | Digital Instruments, Inc. | Scanning stylus atomic force microscope with cantilever tracking and optical access |
| US5381224A (en) * | 1993-08-30 | 1995-01-10 | A. E. Dixon | Scanning laser imaging system |
| US5528426A (en) * | 1994-07-14 | 1996-06-18 | Tti Medical | Laser block beam splitter for microscopes |
| US5784152A (en) * | 1995-03-16 | 1998-07-21 | Bio-Rad Laboratories | Tunable excitation and/or tunable detection microplate reader |
| US5591981A (en) * | 1995-03-16 | 1997-01-07 | Bio-Rad Laboratories, Inc. | Tunable excitation and/or tunable emission fluorescence imaging |
| US5863504A (en) * | 1995-03-16 | 1999-01-26 | Bio-Rad Laboratories, Inc. | Fluorescence imaging instrument utilizing fish |
| JP3526489B2 (en) * | 1995-05-25 | 2004-05-17 | オリンパス株式会社 | Epi-fluorescence microscope |
| US20050100946A1 (en) * | 1995-06-29 | 2005-05-12 | Affymetrix, Inc. | Integrated nucleic acid diagnostic device and method for in-situ confocal microscopy |
| US5981180A (en) * | 1995-10-11 | 1999-11-09 | Luminex Corporation | Multiplexed analysis of clinical specimens apparatus and methods |
| DE69638321D1 (en) | 1995-10-11 | 2011-03-03 | Luminex Corp | SIMULTANEOUS MULTI-ANALYSIS OF CLINICAL SAMPLES |
| US5736330A (en) * | 1995-10-11 | 1998-04-07 | Luminex Corporation | Method and compositions for flow cytometric determination of DNA sequences |
| FR2754341B1 (en) * | 1996-10-04 | 1998-12-24 | Dilor | SPECTRAL ANALYSIS APPARATUS CAPABLE OF WORKING IN MULTIPLE SPECTRAL AREAS OF DIFFERENT WAVELENGTHS |
| US6449562B1 (en) | 1996-10-10 | 2002-09-10 | Luminex Corporation | Multiplexed analysis of clinical specimens apparatus and method |
| US5880473A (en) * | 1997-07-28 | 1999-03-09 | Applied Imaging, Inc. | Multifluor-fluorescence in-situ hybridization (M-FISH) imaging techniques using multiple multiband filters with image registration |
| WO1998017992A2 (en) * | 1996-10-25 | 1998-04-30 | Applied Imaging, Inc. | Multifluor-fluorescence in situ hybridization (m-fish) imaging techniques using multiple multiband filters with image registration |
| US6148114A (en) * | 1996-11-27 | 2000-11-14 | Ultrapointe Corporation | Ring dilation and erosion techniques for digital image processing |
| US6008264A (en) | 1997-04-30 | 1999-12-28 | Laser Med, Inc. | Method for curing polymeric materials, such as those used in dentistry, and for tailoring the post-cure properties of polymeric materials through the use of light source power modulation |
| US6282013B1 (en) | 1997-04-30 | 2001-08-28 | Lasermed, Inc. | System for curing polymeric materials, such as those used in dentistry, and for tailoring the post-cure properties of polymeric materials through the use of light source power modulation |
| WO1999021505A1 (en) | 1997-10-29 | 1999-05-06 | Bisco, Inc. | Dental composite light curing system |
| US6116900A (en) * | 1997-11-17 | 2000-09-12 | Lumachem, Inc. | Binary energizer and peroxide delivery system for dental bleaching |
| US6051835A (en) * | 1998-01-07 | 2000-04-18 | Bio-Rad Laboratories, Inc. | Spectral imaging apparatus and methodology |
| AU2322099A (en) * | 1998-01-16 | 1999-08-02 | Luminex Corporation | Multiplexed analysis of clinical specimens apparatus and methods |
| US6200134B1 (en) | 1998-01-20 | 2001-03-13 | Kerr Corporation | Apparatus and method for curing materials with radiation |
| US6831781B2 (en) | 1998-02-26 | 2004-12-14 | The General Hospital Corporation | Confocal microscopy with multi-spectral encoding and system and apparatus for spectroscopically encoded confocal microscopy |
| WO1999044089A1 (en) | 1998-02-26 | 1999-09-02 | The General Hospital Corporation | Confocal microscopy with multi-spectral encoding |
| JP2003524754A (en) * | 1998-05-16 | 2003-08-19 | ピーイー コーポレイション （エヌワイ） | Apparatus for monitoring the polymerase chain reaction of DNA |
| US6818437B1 (en) * | 1998-05-16 | 2004-11-16 | Applera Corporation | Instrument for monitoring polymerase chain reaction of DNA |
| US7498164B2 (en) | 1998-05-16 | 2009-03-03 | Applied Biosystems, Llc | Instrument for monitoring nucleic acid sequence amplification reaction |
| DE19829944C2 (en) * | 1998-07-04 | 2002-03-28 | Zeiss Carl Jena Gmbh | Method and arrangement for device configuration of a fluorescence laser scanning microscope |
| DE19829981C2 (en) † | 1998-07-04 | 2002-10-17 | Zeiss Carl Jena Gmbh | Method and arrangement for confocal microscopy |
| DE19835070B4 (en) * | 1998-08-04 | 2006-03-16 | Carl Zeiss Jena Gmbh | Arrangement for adjustable wavelength-dependent detection in a fluorescence microscope |
| US6603537B1 (en) * | 1998-08-21 | 2003-08-05 | Surromed, Inc. | Optical architectures for microvolume laser-scanning cytometers |
| DE19842153C2 (en) * | 1998-09-15 | 2003-07-31 | Leica Microsystems | fluorescence microscope |
| JP4270610B2 (en) * | 1998-09-24 | 2009-06-03 | オリンパス株式会社 | Scanning optical microscope |
| US6628385B1 (en) * | 1999-02-05 | 2003-09-30 | Axon Instruments, Inc. | High efficiency, large field scanning microscope |
| US6541778B1 (en) * | 1999-04-23 | 2003-04-01 | Iowa State University Research Foundation, Inc. | Method and apparatus for ceramic analysis |
| US6937330B2 (en) | 1999-04-23 | 2005-08-30 | Ppd Biomarker Discovery Sciences, Llc | Disposable optical cuvette cartridge with low fluorescence material |
| US6157661A (en) * | 1999-05-12 | 2000-12-05 | Laserphysics, Inc. | System for producing a pulsed, varied and modulated laser output |
| WO2000071991A1 (en) * | 1999-05-25 | 2000-11-30 | Biometric Imaging, Inc. | Apparatus and method for optical detection in a limited depth of field |
| US6548796B1 (en) | 1999-06-23 | 2003-04-15 | Regents Of The University Of Minnesota | Confocal macroscope |
| CA2379836A1 (en) * | 1999-07-21 | 2001-02-01 | Aaron B. Kantor | System for microvolume laser scanning cytometry |
| US6687395B1 (en) * | 1999-07-21 | 2004-02-03 | Surromed, Inc. | System for microvolume laser scanning cytometry |
| EP1102101A1 (en) * | 1999-11-22 | 2001-05-23 | Leica Microsystems Heidelberg GmbH | Laser scanning microscope |
| DE10024135B4 (en) * | 2000-01-28 | 2004-07-08 | Leica Microsystems Heidelberg Gmbh | microscope |
| DE10004233B4 (en) * | 2000-02-01 | 2005-02-17 | Leica Microsystems Heidelberg Gmbh | The microscope assemblage |
| US6313433B1 (en) | 2000-04-03 | 2001-11-06 | Universal Laser Systems, Inc | Laser material processing system with multiple laser sources apparatus and method |
| IL135522A (en) | 2000-04-06 | 2005-11-20 | Orbotech Ltd | Optical inspection of laser vias |
| JP2002090628A (en) * | 2000-09-18 | 2002-03-27 | Olympus Optical Co Ltd | Confocal microscope |
| US20040224421A1 (en) * | 2000-06-15 | 2004-11-11 | Deweerd Herman | Bi-directional scanning method |
| DE20122783U1 (en) | 2000-06-17 | 2007-11-15 | Leica Microsystems Cms Gmbh | Arrangement for examining microscopic specimens with a scanning microscope and illumination device for a scanning microscope |
| EP1164402B1 (en) * | 2000-06-17 | 2010-04-28 | Leica Microsystems CMS GmbH | Scanning microscope with multiband illumination and optical element for a scanning microsscope with multiband illumination |
| US6898367B2 (en) | 2000-06-17 | 2005-05-24 | Leica Microsystems Heidelberg Gmbh | Method and instrument for microscopy |
| EP1164406B1 (en) | 2000-06-17 | 2019-04-17 | Leica Microsystems CMS GmbH | Method and device for illuminating an object |
| DE20122782U1 (en) | 2000-06-17 | 2007-11-15 | Leica Microsystems Cms Gmbh | lighting device |
| DE10115590B4 (en) | 2000-06-17 | 2020-11-05 | Leica Microsystems Cms Gmbh | Scanning microscope |
| DE20122791U1 (en) | 2000-06-17 | 2007-11-29 | Leica Microsystems Cms Gmbh | scanning microscope |
| GB2363857A (en) * | 2000-06-23 | 2002-01-09 | Yokogawa Electric Corp | Nipkow disk confocal scanner with optical image separation system |
| DE10044636A1 (en) | 2000-09-08 | 2002-03-21 | Leica Microsystems | Optical arrangement for illuminating objects for confocal scanning microscopes |
| JP4241038B2 (en) | 2000-10-30 | 2009-03-18 | ザ ジェネラル ホスピタル コーポレーション | Optical method and system for tissue analysis |
| US9295391B1 (en) | 2000-11-10 | 2016-03-29 | The General Hospital Corporation | Spectrally encoded miniature endoscopic imaging probe |
| US6787761B2 (en) * | 2000-11-27 | 2004-09-07 | Surromed, Inc. | Median filter for liquid chromatography-mass spectrometry data |
| US20020095260A1 (en) * | 2000-11-28 | 2002-07-18 | Surromed, Inc. | Methods for efficiently mining broad data sets for biological markers |
| DE10065784C2 (en) * | 2000-12-30 | 2003-12-04 | Leica Microsystems | Method for finding contact points between cells in a stimulable microscopic sample during calcium migration and scanning microscope for carrying out the method |
| DE10120425C2 (en) * | 2001-04-26 | 2003-12-18 | Leica Microsystems | scanning microscope |
| EP2333523B1 (en) * | 2001-04-30 | 2020-04-08 | The General Hospital Corporation | Method and apparatus for improving image clarity and sensitivity in optical coherence tomography using dynamic feedback to control focal properties and coherence gating |
| US7865231B2 (en) | 2001-05-01 | 2011-01-04 | The General Hospital Corporation | Method and apparatus for determination of atherosclerotic plaque type by measurement of tissue optical properties |
| JP2003028797A (en) * | 2001-07-11 | 2003-01-29 | Hitachi Software Eng Co Ltd | Fluorescence reader |
| US6873915B2 (en) * | 2001-08-24 | 2005-03-29 | Surromed, Inc. | Peak selection in multidimensional data |
| US20030078739A1 (en) * | 2001-10-05 | 2003-04-24 | Surromed, Inc. | Feature list extraction from data sets such as spectra |
| DE10150542B4 (en) * | 2001-10-12 | 2007-03-29 | Leica Microsystems Cms Gmbh | Method for fluorescence microscopy |
| US6980299B1 (en) * | 2001-10-16 | 2005-12-27 | General Hospital Corporation | Systems and methods for imaging a sample |
| WO2003038503A1 (en) * | 2001-11-02 | 2003-05-08 | Olympus Corporation | Scanning con-focal microscope |
| DE10156506C1 (en) * | 2001-11-16 | 2003-05-22 | Leica Microsystems | Multi-color image forming method and microscope |
| EP1316794A1 (en) * | 2001-11-28 | 2003-06-04 | Cambridge University Technical Services Limited | A dual wavelength optical fluorescence analyser |
| US7158294B2 (en) * | 2001-12-18 | 2007-01-02 | Olympus Optical Co., Ltd. | Laser scanning confocal microscope apparatus, image recording method, and recording medium |
| WO2003060423A2 (en) | 2002-01-11 | 2003-07-24 | The General Hospital Corporation | Apparatus for low coherence ranging |
| US7355716B2 (en) | 2002-01-24 | 2008-04-08 | The General Hospital Corporation | Apparatus and method for ranging and noise reduction of low coherence interferometry LCI and optical coherence tomography OCT signals by parallel detection of spectral bands |
| DE10212554A1 (en) * | 2002-03-16 | 2003-10-30 | Zeiss Carl Jena Gmbh | Arrangement and method for an imaging spectrometer |
| KR100483706B1 (en) * | 2002-04-04 | 2005-04-18 | 바디텍메드 주식회사 | A Apparatus for the Detection of Laser-induced Epifluoresecne |
| DE10217545A1 (en) * | 2002-04-17 | 2003-11-06 | Zeiss Carl Jena Gmbh | Microscope with position detection of changers of optical elements |
| JP2005524833A (en) * | 2002-05-03 | 2005-08-18 | イムニベスト・コーポレイション | Devices and methods for analytical cell imaging |
| AU2003239409A1 (en) * | 2002-05-09 | 2003-11-11 | Surromed, Inc. | Methods for time-alignment of liquid chromatography-mass spectrometry data |
| DE10225838B4 (en) | 2002-06-11 | 2021-10-21 | Leica Microsystems Cms Gmbh | Method for scanning microscopy, scanning microscope and device for coding an illuminating light beam |
| DE10231475A1 (en) | 2002-07-12 | 2004-01-22 | Leica Microsystems Heidelberg Gmbh | Scanning microscope with optical component and optical component |
| DE10231776B4 (en) * | 2002-07-13 | 2021-07-22 | Leica Microsystems Cms Gmbh | Procedure for scanning microscopy and scanning microscope |
| JP2004163413A (en) | 2002-08-28 | 2004-06-10 | Carl-Zeiss-Stiftung Trading As Carl Zeiss | Microscope system and microscope inspection method |
| US7038848B2 (en) * | 2002-12-27 | 2006-05-02 | Olympus Corporation | Confocal microscope |
| DE10302259B3 (en) * | 2003-01-22 | 2004-06-03 | Leica Microsystems Heidelberg Gmbh | Confocal scanning microscope has acousto-optical component for directing partial beam obtained from illumination beam onto monitoring detector for illumination intensity regulation |
| EP2319405B1 (en) | 2003-01-24 | 2013-09-18 | The General Hospital Corporation | System and method for identifying tissue using low-coherence interferometry |
| WO2004088361A2 (en) | 2003-03-31 | 2004-10-14 | The General Hospital Corporation | Speckle reduction in optical coherence tomography by path length encoded angular compounding |
| US8054468B2 (en) | 2003-01-24 | 2011-11-08 | The General Hospital Corporation | Apparatus and method for ranging and noise reduction of low coherence interferometry LCI and optical coherence tomography OCT signals by parallel detection of spectral bands |
| DE10309911B4 (en) | 2003-03-07 | 2021-10-14 | Leica Microsystems Cms Gmbh | Method for determining a longitudinal color defect of a scanning microscope and scanning microscope |
| DE10324478B3 (en) * | 2003-05-30 | 2004-12-09 | Leica Microsystems Heidelberg Gmbh | Device for determining the light output of a light beam and scanning microscope |
| KR101386971B1 (en) * | 2003-06-06 | 2014-04-18 | 더 제너럴 하스피탈 코포레이션 | Process and apparatus for a wavelength tunning source |
| DE10331906B4 (en) * | 2003-07-15 | 2005-06-16 | Leica Microsystems Heidelberg Gmbh | Light source with a microstructured optical element and microscope with light source |
| DE10333388B4 (en) | 2003-07-23 | 2021-09-16 | Leica Microsystems Cms Gmbh | Scanning microscopy and scanning microscope procedures |
| DE10334145A1 (en) * | 2003-07-26 | 2005-02-24 | Leica Microsystems Heidelberg Gmbh | scanning microscope |
| DE10340964A1 (en) | 2003-09-05 | 2005-03-31 | Leica Microsystems Heidelberg Gmbh | Light source with a microstructured optical element |
| JP4756819B2 (en) | 2003-10-21 | 2011-08-24 | オリンパス株式会社 | Scanning microscope system |
| US7733497B2 (en) | 2003-10-27 | 2010-06-08 | The General Hospital Corporation | Method and apparatus for performing optical imaging using frequency-domain interferometry |
| EP1687587B1 (en) * | 2003-11-28 | 2020-01-08 | The General Hospital Corporation | Method and apparatus for three-dimensional spectrally encoded imaging |
| US7248360B2 (en) | 2004-04-02 | 2007-07-24 | Ppd Biomarker Discovery Sciences, Llc | Polychronic laser scanning system and method of use |
| JP4323369B2 (en) * | 2004-04-09 | 2009-09-02 | オリンパス株式会社 | Scanning fluorescence microscope |
| AU2004320269B2 (en) | 2004-05-29 | 2011-07-21 | The General Hospital Corporation | Process, system and software arrangement for a chromatic dispersion compensation using reflective layers in optical coherence tomography (OCT) imaging |
| FR2871358B1 (en) * | 2004-06-14 | 2007-02-09 | Mauna Kea Technologies Soc Par | METHOD AND SYSTEM FOR MICROSCOPIC MULTI-MARKING FIBER FLUORESCENCE IMAGING |
| DE102004030669A1 (en) | 2004-06-24 | 2006-01-19 | Leica Microsystems Cms Gmbh | microscope |
| WO2006014392A1 (en) | 2004-07-02 | 2006-02-09 | The General Hospital Corporation | Endoscopic imaging probe comprising dual clad fibre |
| US8081316B2 (en) | 2004-08-06 | 2011-12-20 | The General Hospital Corporation | Process, system and software arrangement for determining at least one location in a sample using an optical coherence tomography |
| WO2006024014A2 (en) | 2004-08-24 | 2006-03-02 | The General Hospital Corporation | Process, system and software arrangement for measuring a mechanical strain and elastic properties of a sample |
| US8208995B2 (en) | 2004-08-24 | 2012-06-26 | The General Hospital Corporation | Method and apparatus for imaging of vessel segments |
| US7365859B2 (en) * | 2004-09-10 | 2008-04-29 | The General Hospital Corporation | System and method for optical coherence imaging |
| EP2329759B1 (en) | 2004-09-29 | 2014-03-12 | The General Hospital Corporation | System and method for optical coherence imaging |
| DE102004047820A1 (en) | 2004-09-29 | 2006-03-30 | Leica Microsystems Cms Gmbh | Scanning microscope and scanning microscopy method |
| JP5175101B2 (en) * | 2004-10-29 | 2013-04-03 | ザ ジェネラル ホスピタル コーポレイション | System and method for performing Jones matrix based analysis to measure unpolarized polarization parameters using polarization sensitive optical coherence tomography |
| JP5623692B2 (en) * | 2004-11-02 | 2014-11-12 | ザ ジェネラル ホスピタル コーポレイション | Optical fiber rotator, optical system and method for sample imaging |
| US7995210B2 (en) | 2004-11-24 | 2011-08-09 | The General Hospital Corporation | Devices and arrangements for performing coherence range imaging using a common path interferometer |
| JP2008521516A (en) | 2004-11-29 | 2008-06-26 | ザ ジェネラル ホスピタル コーポレイション | Configuration, apparatus, endoscope, catheter, and method for performing optical image generation by simultaneously illuminating and detecting multiple points on a sample |
| US7491502B2 (en) * | 2004-12-17 | 2009-02-17 | The General Hospital Corporation | In vivo flow cytometry system and method |
| US7264794B2 (en) * | 2004-12-17 | 2007-09-04 | The General Hospital | Methods of in vivo cytometry |
| JP2006208681A (en) * | 2005-01-27 | 2006-08-10 | Olympus Corp | Connection unit and optical scanning type fluorescent observation device |
| WO2006092317A1 (en) * | 2005-03-03 | 2006-09-08 | Ese Embedded System Engineering Gmbh | Fluorescence meter |
| US7288098B2 (en) * | 2005-04-14 | 2007-10-30 | Ethicon Endo-Surgery, Inc. | Force limiting mechanism for medical instrument |
| US7740641B2 (en) | 2005-04-14 | 2010-06-22 | Ethicon Endo-Surgery, Inc. | Clip applier with migrational resistance features |
| US8038686B2 (en) | 2005-04-14 | 2011-10-18 | Ethicon Endo-Surgery, Inc. | Clip applier configured to prevent clip fallout |
| US7297149B2 (en) | 2005-04-14 | 2007-11-20 | Ethicon Endo-Surgery, Inc. | Surgical clip applier methods |
| US7686820B2 (en) | 2005-04-14 | 2010-03-30 | Ethicon Endo-Surgery, Inc. | Surgical clip applier ratchet mechanism |
| US7261724B2 (en) * | 2005-04-14 | 2007-08-28 | Ethicon Endo-Surgery, Inc. | Surgical clip advancement mechanism |
| US8523882B2 (en) | 2005-04-14 | 2013-09-03 | Ethicon Endo-Surgery, Inc. | Clip advancer mechanism with alignment features |
| EP2325803A1 (en) | 2005-04-28 | 2011-05-25 | The General Hospital Corporation | Evaluating optical coherence tomography information for an anatomical structure |
| EP1887926B1 (en) * | 2005-05-31 | 2014-07-30 | The General Hospital Corporation | System and method which use spectral encoding heterodyne interferometry techniques for imaging |
| US9060689B2 (en) | 2005-06-01 | 2015-06-23 | The General Hospital Corporation | Apparatus, method and system for performing phase-resolved optical frequency domain imaging |
| ES2354287T3 (en) | 2005-08-09 | 2011-03-11 | The General Hospital Corporation | APPARATUS AND METHOD FOR PERFORMING A DEMODULATION IN QUADRATURE BY POLARIZATION IN OPTICAL COHERENCE TOMOGRAPHY. |
| CN101365375B (en) | 2005-09-29 | 2013-09-11 | 通用医疗公司 | Method and apparatus for optical imaging via spectral encoding |
| US7889348B2 (en) | 2005-10-14 | 2011-02-15 | The General Hospital Corporation | Arrangements and methods for facilitating photoluminescence imaging |
| US8290239B2 (en) * | 2005-10-21 | 2012-10-16 | Orbotech Ltd. | Automatic repair of electric circuits |
| US20080311585A1 (en) * | 2005-11-02 | 2008-12-18 | Affymetrix, Inc. | System and method for multiplex liquid handling |
| US8075852B2 (en) * | 2005-11-02 | 2011-12-13 | Affymetrix, Inc. | System and method for bubble removal |
| US20080038714A1 (en) * | 2005-11-02 | 2008-02-14 | Affymetrix, Inc. | Instrument to Pneumatically Control Lab Cards and Method Thereof |
| US8007267B2 (en) * | 2005-11-02 | 2011-08-30 | Affymetrix, Inc. | System and method for making lab card by embossing |
| US20070099288A1 (en) * | 2005-11-02 | 2007-05-03 | Affymetrix, Inc. | Microfluidic Methods, Devices, and Systems for Fluid Handling |
| EP1971848B1 (en) | 2006-01-10 | 2019-12-04 | The General Hospital Corporation | Systems and methods for generating data based on one or more spectrally-encoded endoscopy techniques |
| US8145018B2 (en) | 2006-01-19 | 2012-03-27 | The General Hospital Corporation | Apparatus for obtaining information for a structure using spectrally-encoded endoscopy techniques and methods for producing one or more optical arrangements |
| PL1973466T3 (en) | 2006-01-19 | 2021-07-05 | The General Hospital Corporation | Ballon imaging catheter |
| US20070223006A1 (en) * | 2006-01-19 | 2007-09-27 | The General Hospital Corporation | Systems and methods for performing rapid fluorescence lifetime, excitation and emission spectral measurements |
| WO2007084959A1 (en) * | 2006-01-20 | 2007-07-26 | The General Hospital Corporation | Systems and methods for providing mirror tunnel microscopy |
| WO2007149603A2 (en) | 2006-02-01 | 2007-12-27 | The General Hospital Corporation | Apparatus for applying a plurality of electro-magnetic radiations to a sample |
| JP5524487B2 (en) | 2006-02-01 | 2014-06-18 | ザ ジェネラル ホスピタル コーポレイション | A method and system for emitting electromagnetic radiation to at least a portion of a sample using a conformal laser treatment procedure. |
| WO2007149601A2 (en) | 2006-02-01 | 2007-12-27 | The General Hospital Corporation | Apparatus for controlling at least one of at least two sections of at least one fiber |
| JP5519152B2 (en) | 2006-02-08 | 2014-06-11 | ザ ジェネラル ホスピタル コーポレイション | Device for acquiring information about anatomical samples using optical microscopy |
| EP1987318B1 (en) | 2006-02-24 | 2015-08-12 | The General Hospital Corporation | Methods and systems for performing angle-resolved fourier-domain optical coherence tomography |
| WO2007109540A2 (en) * | 2006-03-17 | 2007-09-27 | The General Hospital Corporation | Arrangement, method and computer-accessible medium for identifying characteristics of at least a portion of a blood vessel contained within a tissue using spectral domain low coherence interferometry |
| JP5135324B2 (en) | 2006-04-05 | 2013-02-06 | ザ ジェネラル ホスピタル コーポレイション | Method, arrangement and system for polarization sensitive optical frequency domain imaging of samples |
| EP2517616A3 (en) | 2006-05-10 | 2013-03-06 | The General Hospital Corporation | Processes, arrangements and systems for providing frequency domain imaging of a sample |
| WO2007133964A2 (en) * | 2006-05-12 | 2007-11-22 | The General Hospital Corporation | Processes, arrangements and systems for providing a fiber layer thickness map based on optical coherence tomography images |
| CN101589301B (en) | 2006-08-25 | 2012-11-07 | 通用医疗公司 | Apparatus and methods for enhancing optical coherence tomography imaging using volumetric filtering techniques |
| DE102006047816A1 (en) * | 2006-10-07 | 2008-04-17 | Leica Microsystems Cms Gmbh | Method and apparatus for high resolution optical scanning of a sample |
| WO2008049118A2 (en) | 2006-10-19 | 2008-04-24 | The General Hospital Corporation | Apparatus and method for obtaining and providing imaging information associated with at least one portion of a sample and effecting such portion(s) |
| US8155730B2 (en) * | 2006-10-24 | 2012-04-10 | The Research Foundation Of State University Of New York | Composition, method, system, and kit for optical electrophysiology |
| US7911621B2 (en) | 2007-01-19 | 2011-03-22 | The General Hospital Corporation | Apparatus and method for controlling ranging depth in optical frequency domain imaging |
| US7949019B2 (en) | 2007-01-19 | 2011-05-24 | The General Hospital | Wavelength tuning source based on a rotatable reflector |
| EP2602651A3 (en) | 2007-03-23 | 2014-08-27 | The General Hospital Corporation | Methods, arrangements and apparatus for utilizing a wavelength-swept laser using angular scanning and dispersion procedures |
| US10534129B2 (en) | 2007-03-30 | 2020-01-14 | The General Hospital Corporation | System and method providing intracoronary laser speckle imaging for the detection of vulnerable plaque |
| WO2008131082A1 (en) | 2007-04-17 | 2008-10-30 | The General Hospital Corporation | Apparatus and methods for measuring vibrations using spectrally-encoded endoscopy techniques |
| WO2008137693A2 (en) * | 2007-05-04 | 2008-11-13 | The General Hospital Corporation D/B/A Massachusetts General Hospital | Retinal flow cytometry |
| US8115919B2 (en) | 2007-05-04 | 2012-02-14 | The General Hospital Corporation | Methods, arrangements and systems for obtaining information associated with a sample using optical microscopy |
| EP2176647B1 (en) * | 2007-07-27 | 2013-05-15 | Koninklijke Philips Electronics N.V. | Method and system for imaging samples |
| JP5917803B2 (en) | 2007-07-31 | 2016-05-18 | ザ ジェネラル ホスピタル コーポレイション | System and method for emitting a beam scanning pattern for fast Doppler optical frequency domain imaging |
| EP2191254B1 (en) | 2007-08-31 | 2017-07-19 | The General Hospital Corporation | System and method for self-interference fluorescence microscopy, and computer-accessible medium associated therewith |
| HU229592B1 (en) | 2007-09-03 | 2014-02-28 | Univ Szegedi | Tomographic optical microscope system and method for reconstructing the image of an object |
| US20090131801A1 (en) * | 2007-10-12 | 2009-05-21 | The General Hospital Corporation | Systems and processes for optical imaging of luminal anatomic structures |
| WO2009059034A1 (en) | 2007-10-30 | 2009-05-07 | The General Hospital Corporation | System and method for cladding mode detection |
| US11123047B2 (en) | 2008-01-28 | 2021-09-21 | The General Hospital Corporation | Hybrid systems and methods for multi-modal acquisition of intravascular imaging data and counteracting the effects of signal absorption in blood |
| US9332942B2 (en) * | 2008-01-28 | 2016-05-10 | The General Hospital Corporation | Systems, processes and computer-accessible medium for providing hybrid flourescence and optical coherence tomography imaging |
| WO2009120964A2 (en) | 2008-03-27 | 2009-10-01 | The General Hospital Corporation | In vivo flow cytometry based on cellular autofluorescence |
| EP2274572A4 (en) | 2008-05-07 | 2013-08-28 | Gen Hospital Corp | System, method and computer-accessible medium for tracking vessel motion during three-dimensional coronary artery microscopy |
| WO2009155536A2 (en) | 2008-06-20 | 2009-12-23 | The General Hospital Corporation | Fused fiber optic coupler arrangement and method for use thereof |
| WO2010009136A2 (en) | 2008-07-14 | 2010-01-21 | The General Hospital Corporation | Apparatus and methods for color endoscopy |
| DE102008034008B4 (en) * | 2008-07-21 | 2010-07-01 | Carl Zeiss Surgical Gmbh | Filter kit for the observation of fluorescence radiation in biological tissue |
| JP5731394B2 (en) | 2008-12-10 | 2015-06-10 | ザ ジェネラル ホスピタル コーポレイション | System, apparatus and method for extending imaging depth range of optical coherence tomography through optical subsampling |
| WO2010085775A2 (en) | 2009-01-26 | 2010-07-29 | The General Hospital Corporation | System, method and computer-accessible medium for providing wide-field superresolution microscopy |
| CN102308444B (en) | 2009-02-04 | 2014-06-18 | 通用医疗公司 | Apparatus and method for utilization of a high-speed optical wavelength tuning source |
| US9351642B2 (en) | 2009-03-12 | 2016-05-31 | The General Hospital Corporation | Non-contact optical system, computer-accessible medium and method for measurement at least one mechanical property of tissue using coherent speckle technique(s) |
| US9072572B2 (en) | 2009-04-02 | 2015-07-07 | Kerr Corporation | Dental light device |
| US9066777B2 (en) | 2009-04-02 | 2015-06-30 | Kerr Corporation | Curing light device |
| BR112012001042A2 (en) | 2009-07-14 | 2016-11-22 | Gen Hospital Corp | fluid flow measurement equipment and method within anatomical structure. |
| US8262679B2 (en) | 2009-10-09 | 2012-09-11 | Ethicon Endo-Surgery, Inc. | Clip advancer |
| US8267945B2 (en) | 2009-10-09 | 2012-09-18 | Ethicon Endo-Surgery, Inc. | Clip advancer with lockout mechanism |
| ES2831223T3 (en) | 2010-03-05 | 2021-06-07 | Massachusetts Gen Hospital | Apparatus for providing electromagnetic radiation to a sample |
| US9069130B2 (en) | 2010-05-03 | 2015-06-30 | The General Hospital Corporation | Apparatus, method and system for generating optical radiation from biological gain media |
| US9557154B2 (en) | 2010-05-25 | 2017-01-31 | The General Hospital Corporation | Systems, devices, methods, apparatus and computer-accessible media for providing optical imaging of structures and compositions |
| US9795301B2 (en) | 2010-05-25 | 2017-10-24 | The General Hospital Corporation | Apparatus, systems, methods and computer-accessible medium for spectral analysis of optical coherence tomography images |
| EP2575591A4 (en) | 2010-06-03 | 2017-09-13 | The General Hospital Corporation | Apparatus and method for devices for imaging structures in or at one or more luminal organs |
| US9510758B2 (en) | 2010-10-27 | 2016-12-06 | The General Hospital Corporation | Apparatus, systems and methods for measuring blood pressure within at least one vessel |
| WO2012112911A2 (en) | 2011-02-17 | 2012-08-23 | University Of Massachusetts - Lowell | Devices and methods for optical pathology |
| DE102011016138A1 (en) * | 2011-03-30 | 2012-10-04 | Karl Storz Gmbh & Co. Kg | Device for fluorescence diagnosis |
| WO2012149175A1 (en) | 2011-04-29 | 2012-11-01 | The General Hospital Corporation | Means for determining depth-resolved physical and/or optical properties of scattering media |
| WO2013013049A1 (en) | 2011-07-19 | 2013-01-24 | The General Hospital Corporation | Systems, methods, apparatus and computer-accessible-medium for providing polarization-mode dispersion compensation in optical coherence tomography |
| US10241028B2 (en) | 2011-08-25 | 2019-03-26 | The General Hospital Corporation | Methods, systems, arrangements and computer-accessible medium for providing micro-optical coherence tomography procedures |
| EP2769491A4 (en) | 2011-10-18 | 2015-07-22 | Gen Hospital Corp | Apparatus and methods for producing and/or providing recirculating optical delay(s) |
| WO2013059432A1 (en) | 2011-10-19 | 2013-04-25 | Ethicon Endo-Surgery, Inc. | Clip applier adapted for use with a surgical robot |
| WO2013148306A1 (en) | 2012-03-30 | 2013-10-03 | The General Hospital Corporation | Imaging system, method and distal attachment for multidirectional field of view endoscopy |
| WO2013177154A1 (en) | 2012-05-21 | 2013-11-28 | The General Hospital Corporation | Apparatus, device and method for capsule microscopy |
| US8964183B2 (en) * | 2012-05-31 | 2015-02-24 | General Electric Company | Systems and methods for screening of biological samples |
| JP6227652B2 (en) | 2012-08-22 | 2017-11-08 | ザ ジェネラル ホスピタル コーポレイション | System, method, and computer-accessible medium for fabricating a miniature endoscope using soft lithography |
| WO2014120791A1 (en) | 2013-01-29 | 2014-08-07 | The General Hospital Corporation | Apparatus, systems and methods for providing information regarding the aortic valve |
| US11179028B2 (en) | 2013-02-01 | 2021-11-23 | The General Hospital Corporation | Objective lens arrangement for confocal endomicroscopy |
| JP6378311B2 (en) | 2013-03-15 | 2018-08-22 | ザ ジェネラル ホスピタル コーポレイション | Methods and systems for characterizing objects |
| US9347852B1 (en) | 2013-05-08 | 2016-05-24 | Thomas DiMatteo | Microscope illumination diagnostic cube |
| WO2014186353A1 (en) | 2013-05-13 | 2014-11-20 | The General Hospital Corporation | Detecting self-interefering fluorescence phase and amplitude |
| EP3021735A4 (en) | 2013-07-19 | 2017-04-19 | The General Hospital Corporation | Determining eye motion by imaging retina. with feedback |
| WO2015009932A1 (en) | 2013-07-19 | 2015-01-22 | The General Hospital Corporation | Imaging apparatus and method which utilizes multidirectional field of view endoscopy |
| EP3025173B1 (en) | 2013-07-26 | 2021-07-07 | The General Hospital Corporation | Apparatus with a laser arrangement utilizing optical dispersion for applications in fourier-domain optical coherence tomography |
| WO2015087824A1 (en) * | 2013-12-09 | 2015-06-18 | 株式会社ニコン | Optical apparatus, measuring apparatus, measuring method, screening apparatus, and screening method |
| US9733460B2 (en) | 2014-01-08 | 2017-08-15 | The General Hospital Corporation | Method and apparatus for microscopic imaging |
| WO2015116986A2 (en) | 2014-01-31 | 2015-08-06 | The General Hospital Corporation | System and method for facilitating manual and/or automatic volumetric imaging with real-time tension or force feedback using a tethered imaging device |
| WO2015153982A1 (en) | 2014-04-04 | 2015-10-08 | The General Hospital Corporation | Apparatus and method for controlling propagation and/or transmission of electromagnetic radiation in flexible waveguide(s) |
| DE102014008243A1 (en) * | 2014-05-27 | 2015-12-03 | Carl Zeiss Meditec Ag | Fluorescence observation system and optical filter system therefor |
| WO2016015052A1 (en) | 2014-07-25 | 2016-01-28 | The General Hospital Corporation | Apparatus, devices and methods for in vivo imaging and diagnosis |
| DE102014016850B9 (en) | 2014-11-13 | 2017-07-27 | Carl Zeiss Meditec Ag | Optical system for fluorescence observation |
| DE102015011429B9 (en) * | 2015-09-01 | 2020-01-09 | Carl Zeiss Meditec Ag | Optical filter system and fluorescence observation system |
| CN108351301B (en) * | 2015-09-02 | 2021-03-09 | 英思克斯公司 | System and method for color imaging |
| CN108474736B (en) | 2015-11-05 | 2022-01-25 | 英思克斯公司 | System and method for optogenetic imaging |
| DE102018114695B9 (en) * | 2018-06-19 | 2020-05-28 | Carl Zeiss Meditec Ag | Filter set, system and method for the simultaneous excitation and observation of protoporphyrin IX and fluorescein |
| DE102019101773B9 (en) * | 2019-01-24 | 2021-11-25 | Carl Zeiss Meditec Ag | Microscopy system and method for operating a microscopy system |
| EP3907497B1 (en) * | 2020-05-08 | 2023-08-02 | Leica Microsystems CMS GmbH | Apparatus and method for displaying and/or printing images of a specimen including a fluorophore |
| CN112859315A (en) * | 2021-01-11 | 2021-05-28 | 北京大学 | Multicolor dual-mode structured light illumination microscopic imaging system and imaging method thereof |
Family Cites Families (20)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| SE455646B (en) * | 1984-10-22 | 1988-07-25 | Radians Innova Ab | FLUORESCENT DEVICE |
| US4689491A (en) * | 1985-04-19 | 1987-08-25 | Datasonics Corp. | Semiconductor wafer scanning system |
| JPS62138819A (en) * | 1985-12-13 | 1987-06-22 | Hitachi Ltd | Scanning type laser microscope |
| GB8531011D0 (en) * | 1985-12-17 | 1986-01-29 | Medical Res Council | Confocal scanning microscope |
| US4710635A (en) * | 1986-04-14 | 1987-12-01 | Becton, Dickinson And Company | Dual laser excitation from single laser source |
| EP0267278A4 (en) * | 1986-05-13 | 1989-12-19 | Richard Kennedy | Mixing device. |
| US4684602A (en) * | 1986-06-30 | 1987-08-04 | Eastman Kodak Company | Multicolor laser recording method and element |
| US4745285A (en) * | 1986-08-21 | 1988-05-17 | Becton Dickinson And Company | Multi-color fluorescence analysis with single wavelength excitation |
| US4791310A (en) * | 1986-10-02 | 1988-12-13 | Syracuse University | Fluorescence microscopy |
| GB8626576D0 (en) * | 1986-11-06 | 1986-12-10 | Amersham Int Plc | Imaging method |
| JP2836829B2 (en) * | 1987-03-27 | 1998-12-14 | ザ ボード オブ トラスティーズ オブ ザ リーランド スタンフォード ジュニア ユニバーシティ | Scanning confocal optical microscope |
| US4847823A (en) * | 1987-06-19 | 1989-07-11 | Siscan Systems, Inc. | Method and apparatus for reading or measuring magneto-optical storage media using pinhole aperture |
| CS263329B1 (en) * | 1987-07-24 | 1989-04-14 | Petran Mojmir | Light disjoining system |
| US4884881A (en) * | 1987-11-16 | 1989-12-05 | Washington University | Single aperture confocal scanning epi-illumination microscope |
| US4884880A (en) * | 1987-11-16 | 1989-12-05 | Washington University | Kit for converting a standard microscope into a single aperture confocal scanning epi-illumination microscope |
| US4802748A (en) * | 1987-12-14 | 1989-02-07 | Tracor Northern, Inc. | Confocal tandem scanning reflected light microscope |
| FR2626383B1 (en) * | 1988-01-27 | 1991-10-25 | Commissariat Energie Atomique | EXTENDED FIELD SCAN AND DEPTH CONFOCAL OPTICAL MICROSCOPY AND DEVICES FOR CARRYING OUT THE METHOD |
| EP1245987B1 (en) * | 1988-07-13 | 2008-01-23 | Optiscan Pty Ltd | Scanning confocal microscope |
| JP2513862B2 (en) * | 1988-10-11 | 1996-07-03 | イー・アイ・デュポン・ドウ・ヌムール・アンド・カンパニー | Scanning laser microscope device |
| US4972258A (en) * | 1989-07-31 | 1990-11-20 | E. I. Du Pont De Nemours And Company | Scanning laser microscope system and methods of use |
-
1990
- 1990-08-10 US US07/565,625 patent/US5127730A/en not_active Expired - Lifetime
-
1991
- 1991-01-28 WO PCT/US1991/000607 patent/WO1992002839A1/en active IP Right Grant
- 1991-01-28 DK DK91905729T patent/DK0495930T3/en active
- 1991-01-28 CA CA002067188A patent/CA2067188C/en not_active Expired - Lifetime
- 1991-01-28 AT AT91905729T patent/ATE179527T1/en not_active IP Right Cessation
- 1991-01-28 DE DE69131176T patent/DE69131176T2/en not_active Expired - Lifetime
- 1991-01-28 EP EP91905729A patent/EP0495930B1/en not_active Expired - Lifetime
- 1991-01-28 JP JP3505950A patent/JP2824462B2/en not_active Expired - Lifetime
- 1991-01-28 DE DE199191905729T patent/DE495930T1/en active Pending
- 1991-01-28 ES ES91905729T patent/ES2133283T3/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| DE69131176T2 (en) | 1999-12-30 |
| WO1992002839A1 (en) | 1992-02-20 |
| EP0495930A1 (en) | 1992-07-29 |
| EP0495930B1 (en) | 1999-04-28 |
| DK0495930T3 (en) | 1999-11-08 |
| DE495930T1 (en) | 1993-02-25 |
| ES2133283T3 (en) | 1999-09-16 |
| DE69131176D1 (en) | 1999-06-02 |
| US5127730A (en) | 1992-07-07 |
| JP2824462B2 (en) | 1998-11-11 |
| ATE179527T1 (en) | 1999-05-15 |
| CA2067188A1 (en) | 1992-02-11 |
| JPH05501458A (en) | 1993-03-18 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2067188C (en) | Multi-color laser scanning confocal imaging system | |
| US5304810A (en) | Confocal scanning optical microscope | |
| US6462345B1 (en) | Process and arrangement for confocal microscopy | |
| White et al. | Fluorescence techniques for drug delivery research: theory and practice | |
| US7474462B2 (en) | Microscope with evanescent wave illumination | |
| Straub et al. | Fluorescence lifetime three-dimensional microscopy with picosecond precision using a multifocal multiphoton microscope | |
| US6169289B1 (en) | Signal enhancement for fluorescence microscopy | |
| US8704196B2 (en) | Combination microscopy | |
| Wells et al. | Quantitative fluorescence imaging with laser scanning confocal microscopy | |
| US7298551B2 (en) | Method and arrangement for changing the spectral composition and/or intensity of illumination light and/or specimen light in an adjustable manner | |
| US6961124B2 (en) | Method for examining a specimen, and scanning microscope system | |
| WO1996006369A2 (en) | Improving resolution in scanned optical systems | |
| Wokosin et al. | Optical workstation with concurrent, independent multiphoton imaging and experimental laser microbeam capabilities | |
| Hanley et al. | Optical sectioning fluorescence spectroscopy in a programmable array microscope | |
| US20050006597A1 (en) | Arrangement for the optical detection of light radiation which is excited and/or backscattered in a specimen with a double-objective arrangement | |
| Ploem | Fluorescence microscopy | |
| US6717726B2 (en) | Method for generating a multicolor image, and microscope | |
| Rai et al. | The basics of confocal microscopy | |
| US6806953B2 (en) | Method for fluorescence microscopy, and fluorescence microscope | |
| US7333207B2 (en) | Confocal 4-pi microscope and method for confocal 4-pi microscopy | |
| Amos et al. | Direct view confocal imaging systems using a slit aperture | |
| JP2907571B2 (en) | Laser scanning fluorescence microscope | |
| Amos | Instruments for fluorescence imaging | |
| JP2006527858A (en) | Method for fluorescence microscopy | |
| Stanley | [17] Filters and mirrors for applications in fluorescence microscopy |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |