USRE43702E1 - Microscope with heightened resolution and linear scanning - Google Patents
Microscope with heightened resolution and linear scanning Download PDFInfo
- Publication number
- USRE43702E1 USRE43702E1 US12/973,130 US97313010A USRE43702E US RE43702 E1 USRE43702 E1 US RE43702E1 US 97313010 A US97313010 A US 97313010A US RE43702 E USRE43702 E US RE43702E
- Authority
- US
- United States
- Prior art keywords
- sample
- illumination light
- microscope
- periodic structure
- microscope according
- 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.)
- Active
Links
- 230000000737 periodic effect Effects 0.000 claims abstract description 18
- 230000001427 coherent effect Effects 0.000 claims abstract description 13
- 238000005286 illumination Methods 0.000 claims description 55
- 238000000034 method Methods 0.000 claims description 31
- 230000005284 excitation Effects 0.000 claims description 17
- 230000003287 optical effect Effects 0.000 claims description 15
- 230000000694 effects Effects 0.000 claims description 12
- 238000003384 imaging method Methods 0.000 claims description 11
- LFEUVBZXUFMACD-UHFFFAOYSA-H lead(2+);trioxido(oxo)-$l^{5}-arsane Chemical compound [Pb+2].[Pb+2].[Pb+2].[O-][As]([O-])([O-])=O.[O-][As]([O-])([O-])=O LFEUVBZXUFMACD-UHFFFAOYSA-H 0.000 claims description 11
- 230000008569 process Effects 0.000 claims description 11
- 230000002123 temporal effect Effects 0.000 claims description 4
- 230000008054 signal transmission Effects 0.000 claims description 3
- 230000025563 intercellular transport Effects 0.000 claims description 2
- 210000005036 nerve Anatomy 0.000 claims description 2
- 230000001537 neural effect Effects 0.000 claims description 2
- 230000018109 developmental process Effects 0.000 claims 1
- 230000005281 excited state Effects 0.000 claims 1
- 210000003205 muscle Anatomy 0.000 claims 1
- 230000001360 synchronised effect Effects 0.000 claims 1
- 230000005855 radiation Effects 0.000 description 42
- 239000000523 sample Substances 0.000 description 24
- 210000004027 cell Anatomy 0.000 description 18
- 239000000975 dye Substances 0.000 description 14
- 238000004458 analytical method Methods 0.000 description 12
- 210000001747 pupil Anatomy 0.000 description 12
- 238000001514 detection method Methods 0.000 description 11
- 238000010276 construction Methods 0.000 description 8
- 108091006146 Channels Proteins 0.000 description 7
- 238000011835 investigation Methods 0.000 description 7
- 230000000903 blocking effect Effects 0.000 description 6
- 230000003595 spectral effect Effects 0.000 description 6
- 210000001519 tissue Anatomy 0.000 description 6
- 238000004061 bleaching Methods 0.000 description 5
- 210000002569 neuron Anatomy 0.000 description 5
- 239000000835 fiber Substances 0.000 description 4
- 238000000799 fluorescence microscopy Methods 0.000 description 4
- 238000000386 microscopy Methods 0.000 description 4
- 241001465754 Metazoa Species 0.000 description 3
- 238000010521 absorption reaction Methods 0.000 description 3
- 238000013459 approach Methods 0.000 description 3
- 230000008859 change Effects 0.000 description 3
- 238000011161 development Methods 0.000 description 3
- 238000002474 experimental method Methods 0.000 description 3
- 230000003993 interaction Effects 0.000 description 3
- 230000004807 localization Effects 0.000 description 3
- 210000004498 neuroglial cell Anatomy 0.000 description 3
- 230000007935 neutral effect Effects 0.000 description 3
- 230000002269 spontaneous effect Effects 0.000 description 3
- 241000699660 Mus musculus Species 0.000 description 2
- 238000001069 Raman spectroscopy Methods 0.000 description 2
- 241000700159 Rattus Species 0.000 description 2
- 230000004075 alteration Effects 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 2
- RYYVLZVUVIJVGH-UHFFFAOYSA-N caffeine Chemical compound CN1C(=O)N(C)C(=O)C2=C1N=CN2C RYYVLZVUVIJVGH-UHFFFAOYSA-N 0.000 description 2
- 230000001413 cellular effect Effects 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 2
- 238000004624 confocal microscopy Methods 0.000 description 2
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000002376 fluorescence recovery after photobleaching Methods 0.000 description 2
- 238000002866 fluorescence resonance energy transfer Methods 0.000 description 2
- 150000002500 ions Chemical class 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 238000002360 preparation method Methods 0.000 description 2
- 108090000623 proteins and genes Proteins 0.000 description 2
- 102000004169 proteins and genes Human genes 0.000 description 2
- 238000004621 scanning probe microscopy Methods 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- 238000011830 transgenic mouse model Methods 0.000 description 2
- 230000032258 transport Effects 0.000 description 2
- 102000010637 Aquaporins Human genes 0.000 description 1
- 108010063290 Aquaporins Proteins 0.000 description 1
- 102000014914 Carrier Proteins Human genes 0.000 description 1
- 201000008808 Fibrosarcoma Diseases 0.000 description 1
- 108010043121 Green Fluorescent Proteins Proteins 0.000 description 1
- 101001023784 Heteractis crispa GFP-like non-fluorescent chromoprotein Proteins 0.000 description 1
- LPHGQDQBBGAPDZ-UHFFFAOYSA-N Isocaffeine Natural products CN1C(=O)N(C)C(=O)C2=C1N(C)C=N2 LPHGQDQBBGAPDZ-UHFFFAOYSA-N 0.000 description 1
- 102000004856 Lectins Human genes 0.000 description 1
- 108090001090 Lectins Proteins 0.000 description 1
- 206010027476 Metastases Diseases 0.000 description 1
- 241000699670 Mus sp. Species 0.000 description 1
- 102000004279 Oxytocin receptors Human genes 0.000 description 1
- 108090000876 Oxytocin receptors Proteins 0.000 description 1
- 238000001530 Raman microscopy Methods 0.000 description 1
- 230000004913 activation Effects 0.000 description 1
- 230000006978 adaptation Effects 0.000 description 1
- 230000003044 adaptive effect Effects 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 238000005452 bending Methods 0.000 description 1
- 108091008324 binding proteins Proteins 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 229960001948 caffeine Drugs 0.000 description 1
- VJEONQKOZGKCAK-UHFFFAOYSA-N caffeine Natural products CN1C(=O)N(C)C(=O)C2=C1C=CN2C VJEONQKOZGKCAK-UHFFFAOYSA-N 0.000 description 1
- 210000000170 cell membrane Anatomy 0.000 description 1
- 230000001143 conditioned effect Effects 0.000 description 1
- 230000021615 conjugation Effects 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 238000009792 diffusion process Methods 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 238000002839 fiber optic waveguide Methods 0.000 description 1
- 210000002950 fibroblast Anatomy 0.000 description 1
- 238000002073 fluorescence micrograph Methods 0.000 description 1
- 108010021843 fluorescent protein 583 Proteins 0.000 description 1
- 230000005283 ground state Effects 0.000 description 1
- 210000001320 hippocampus Anatomy 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 230000007794 irritation Effects 0.000 description 1
- 239000002523 lectin Substances 0.000 description 1
- 238000010859 live-cell imaging Methods 0.000 description 1
- 230000007774 longterm Effects 0.000 description 1
- 239000011159 matrix material Substances 0.000 description 1
- 230000001404 mediated effect Effects 0.000 description 1
- 230000009401 metastasis Effects 0.000 description 1
- 210000000274 microglia Anatomy 0.000 description 1
- 230000004899 motility Effects 0.000 description 1
- 210000000663 muscle cell Anatomy 0.000 description 1
- 230000003387 muscular Effects 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 239000013307 optical fiber Substances 0.000 description 1
- 238000012634 optical imaging Methods 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 108010054624 red fluorescent protein Proteins 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 230000000284 resting effect Effects 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 229920006395 saturated elastomer Polymers 0.000 description 1
- 238000004611 spectroscopical analysis Methods 0.000 description 1
- 230000001629 suppression Effects 0.000 description 1
- 238000003786 synthesis reaction Methods 0.000 description 1
- 238000012546 transfer Methods 0.000 description 1
- 230000009261 transgenic effect Effects 0.000 description 1
- 230000000472 traumatic effect Effects 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
- 108091005957 yellow fluorescent proteins Proteins 0.000 description 1
Images
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
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
- G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
- G01N21/64—Fluorescence; Phosphorescence
- G01N21/645—Specially adapted constructive features of fluorimeters
- G01N21/6456—Spatial resolved fluorescence measurements; Imaging
- G01N21/6458—Fluorescence microscopy
-
- 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
- G02B21/0036—Scanning details, e.g. scanning stages
-
- 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
- G02B21/0036—Scanning details, e.g. scanning stages
- G02B21/0044—Scanning details, e.g. scanning stages moving apertures, e.g. Nipkow disks, rotating lens arrays
-
- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B21/00—Microscopes
- G02B21/24—Base structure
- G02B21/248—Base structure objective (or ocular) turrets
Definitions
- FIG. 1 is a schematic drawing showing a laser scanning microscope.
- FIG. 2 shows how the zoom optics of the microscope of FIG. 1 can be used to select a region of interest within the maximum available scan field.
- FIG. 3 is a schematic drawing showing a second possible construction for a laser scanning microscope in which a Nipkow disk approach is realized.
- FIG. 4 is a schematic drawing showing a third possible construction for a laser scanning microscope with multiple-point scanning.
- FIG. 5 is a schematic drawing showing a light source arranged behind a grid.
- FIG. 6 is a diagram showing how an interference field of the ⁇ 1 st , 0 th , or 1 st order is formed at an amplitude grid G in transmission during irradiation with laser light.
- FIG. 7 is a diagram showing a beam line presented in the X-Z direction, which illuminates the sample homogenously in the direction of the arrow along the X axis.
- FIG. 1 schematically shows a laser scanning microscope 1 comprising essentially four components: a radiation source module 2 that generates excitation radiation for laser scanning microscopy; a scanning module 3 that conditions the excitation radiation and suitably deflects it for scanning over a sample; a microscope module 4 , for the sake of simplicity shown only schematically, that directs the scanning radiation prepared by the scan module in a microscopic beam path onto a sample; and a detector module 5 that receives and detects optical radiation from the sample.
- Detector module 5 can, as shown in FIG. 1 , be configured so as to be spectrally multichanneled.
- Radiation source module 2 generates illumination radiation that is suitable for the laser scanning microscopy, i.e., in particular radiation that can trigger fluorescence.
- the radiation source module has several radiation sources for this purpose.
- two lasers 6 and 7 are provided in radiation source module 2 , downstream of which a light valve 8 and an attenuator 9 is arranged and which couple their radiation via a coupling point 10 into a fiber optical waveguide 11 .
- Light valve 8 acts as a deflector with which a reduction of radiation can be effected without it being necessary to switch off the operation of the lasers in laser unit 6 or 7 themselves.
- Light valve 8 by way of example is configured as an AOTF which in order to switch off radiation deflects the laser beam prior to injection in optical fiber waveguide 11 in the direction of a not-depicted light trap.
- laser unit 6 has 3 lasers B, C, D, while laser unit 7 contains only one laser A.
- the depiction thus is exemplary for a combination of single and multiple wave-length lasers which individually or also jointly are coupled to one or more fibers. The coupling can also take place over several fibers simultaneously, the radiation of which subsequently is mixed through a color uniter following passage through an adapting optic. It is thus possible to use extremely varied wave lengths or ranges for the excitation radiation.
- the radiation coupled into fiber optic waveguide 11 is drawn together by means of movable collimation optics 12 and 13 through radiation uniting mirrors 14 , 15 and is changed with respect to the radiation profile in a beam-forming unit.
- Collimators 12 , 13 collimate the radiation brought in from radiation source module 2 into scan module 3 into an infinite beam path. This takes place advantageously in each case with the aid of a single lens which as a result of moving along the optical axis under the control of (a not-depicted) central steering unit has a focusing function in that the distance between collimator 12 , 13 and the respective end of the fiber optic is modifiable.
- the beam-forming unit From the radially symmetric Gaussian profiled laser beam, as is present after beam uniting mirrors 14 , 15 , the beam-forming unit, which will be explained in detail later, generates a linear beam that no longer is radially symmetrical but rather is suited in cross section to generate a rectangular illuminating field.
- This illuminating beam which is also designated as being line-shaped serves as triggering radiation and is conducted via a main color splitter 17 and a yet to be described zoom optic to a scanner 18 .
- the main color splitter will be discussed later, but it should be mentioned at this point that it has the function of separating the sample radiation returning from microscope module 4 from the triggering radiation.
- Scanner 18 deflects the line-shaped beam in one or two axes, after which it is bundled through a scanning objective lens 19 and a tube-shaped lens and an objective lens of microscope module 4 into a focus (not shown) which is situated in a preparation or in a sample.
- Optical imaging takes place such that the sample is illuminated in a focal line with triggering radiation.
- Fluorescence radiation excited in this manner in the line-shaped focus arrives through objective lens and tubular lens of microscope module 4 and scanning objective lens 19 back to scanner 18 so that in the reverse direction there again is a resting beam behind scanner 18 . It is therefore also said that the scanner 18 de-scans the fluorescence radiation.
- Main color splitter 17 allows the fluorescence radiation in other wave length ranges than the excitation radiation to pass so that it can be redirected via a redirecting mirror (not shown) in the detector module 5 and can then be analyzed.
- detector module 5 has several spectral channels, i.e., the fluorescence radiation coming from the redirecting mirror is split in a secondary color splitter 25 into two spectral channels.
- Each spectral channel has a slit diaphragm 26 which realizes a confocal or partially confocal image with respect to a sample (not shown) and the size of which slit diaphragm establishes the depth of focus with which the fluorescence can be detected.
- the geometry of slit diaphragm 26 thus determines the cutting plane within the (thick) preparation from which fluorescence radiation is detected.
- Slit diaphragm 26 is arranged behind a blocking filter 27 that blocks out undesired excitation radiation which entered into detector module 5 .
- the radiation separated out in this manner which originated from a certain depth section and was fanned out linearly is then analyzed by a suitable detector 28 .
- the second spectral detection channel which likewise comprises a slit diaphragm 26 a, a blocking filter 27 a, and a detector 28 a, is also constructed analogous to the depicted color channel.
- a confocal slit aperture in detector module 5 is only by way of example.
- a single-point scanner can of course also be realized.
- Slit diaphragms 26 , 26 a are then replaced by apertured diaphragms and the beam-forming unit can be omitted.
- all optics are configured radially symmetrically for such a construction style.
- any desired multiple-point arrangements such as point-cloud or Nipkow-disk concepts can be used as will be explained later with the aid of FIGS. 3 and 4 .
- the Gaussian beam bundles present behind the movable, i.e., sliding collimators 12 and 13 are united through a ladder of mirrors in the form of beam-uniting mirrors 14 , 16 and then in the construction depicted with confocal slit diaphragm are converted into a beam bundle with rectangular beam cross section.
- a cylinder telescope 37 that is arranged behind an aspherical unit 38 which is followed by cylinder optics 39 is utilized in the beam-forming unit.
- the illumination arrangement with aspherical unit 38 can serve the purpose of uniform filling of a pupil between a tubular lens and an objective lens. In this way the optical resolution of the objective lens can be fully utilized.
- This variant thus is also advantageous in a single-point or multiple-point scanning microscope system, for example in a line scanning system (in the case of the latter in addition to the axis in which focusing upon or into the sample takes place).
- the excitation radiation by way of example conditioned linearly is directed onto main color splitter 17 .
- the latter is configured as a spectrally neutral splitter mirror in accordance with DE 10257537 A1, the full disclosure content of which is incorporated here.
- the term “color splitter” thus also comprises non-spectrally acting splitter systems.
- a homogenous neutral splitter for example 50/50, 70/30, 80/20, or the like
- a dichroitic splitter can also be used.
- the main color splitter preferably is provided by a mechanism which facilitates an easy change, for example through a corresponding splitter wheel that contains individual interchangeable splitters.
- the dichroitic main color splitter is particularly advantageous if coherent, i.e., directional radiation is to be detected such as, for example, reflection, Stokesian or anti-Stokesian Raman spectroscopy, coherent Raman processes of relatively high order, general parametric non-linear optical processes such as second harmonic generation, third harmonic generation, sum frequency generation, and double and multiple photon absorption or fluorescence.
- coherent, i.e., directional radiation such as, for example, reflection, Stokesian or anti-Stokesian Raman spectroscopy, coherent Raman processes of relatively high order, general parametric non-linear optical processes such as second harmonic generation, third harmonic generation, sum frequency generation, and double and multiple photon absorption or fluorescence.
- Several of these methods of non-linear optical spectroscopy require the use of two or more laser beams which are superimposed collinearly. In so doing, the depicted beam unification of the radiation of several lasers proves to be particularly advantageous.
- the dichroitic beam divider which is widely
- the excitation radiation or illumination radiation is brought to scanner 18 through motor-controlled zoom optics 41 .
- zoom optics 41 are advantageous in which the pupil position remains in a continuous tuning process during adjustment of the focus location and of the imaging scale.
- the three motorized degrees of freedom depicted in FIG. 1 , symbolized by arrows, of zoom optics 41 correspond precisely to the number of degrees of freedom which are provided for adaptation of the three parameters imaging scale, focus location, and pupil location.
- zoom optics 41 at the exit-side pupil of which a fixed diaphragm 42 is arranged.
- diaphragm 42 can also be predetermined through the limitation of the mirror surface of scanner 18 .
- Output-side diaphragm 42 with zoom optics 41 causes a predefined pupil diameter to always be imaged on scanning objective lens 19 independent of the setting of the zoom enlargement.
- the objective lens pupil continues to be fully illuminated regardless of the setting of zoom optics 41 .
- the use of a self-contained diaphragm 42 advantageously prevents the occurrence of undesired scatter radiation in the area of scanner 18 .
- cylinder telescope 37 which is likewise motorized and is arranged in front of aspherical unit 38 .
- this is selected as a result of a compact construction but does not have to be such.
- cylinder telescope 37 is automatically swung into the optical beam path. If zoom objective lens 41 is made smaller, incomplete illumination of aperture diaphragm 42 is prevented. Swivelable cylinder telescope 37 thus ensures that even at zoom factors smaller than 1, i.e., independent of the setting of zoom optics 41 an illumination line of constant length is always present at the site of the objective lens pupil. In comparison to a simple visual field zoom, laser performance losses in the illumination beam are thus avoided.
- remote controllable adjustment elements are also provided in detector module 5 of the laser scanning microscope of FIG. 1 .
- round optics 44 as well as cylinder optics 39 by way of example are provided in front of the slit diaphragm and cylinder optics 39 are provided directly in front of detector 28 , each of which can be shifted in axial direction by motor.
- correction unit 40 In addition to compensation, a correction unit 40 is provided which will be described briefly below.
- blocking filter 27 is arranged in front of second cylinder lens 39 , blocking filter 27 having suitable spectral properties in order to allow only the desired fluorescence radiation to reach detector 28 , 28 a.
- a change of color splitter 25 of blocking filter 27 unavoidably is accompanied by a certain tilt error or wedge error upon swiveling into place.
- the color splitter can cause an error between the sample range and slit diaphragm 26
- blocking filter 27 can cause an error between slit diaphragm 26 and detector 28 .
- a plane-parallel plate 40 is arranged between round optics 44 and slit diaphragm 26 , i.e., in the imaging beam path between the sample and detector 28 which under the control of a controller can be brought into various inclination positions.
- Plane-parallel plate 40 in addition is adjustably mounted in a suitable holding device.
- the second spectral detection channel likewise comprises a plane-parallel plate 40 a arranged between round Optics 44 a and slit diaphragm 26 a, i.e., in the imaging beam path between the sample and detector 28 a.
- FIG. 2 shows how with the aid of zoom optics 41 , a region of interest ROI can be selected within the maximum scan field SF which is available. If one allows the steering of scanner 18 to be such that the amplitude does not change, as is required by way of example for resonance scanners, an enlargement greater than 1.0 set at the zoom optics will cause a narrowing of the selected region of interest ROI centered around the optical axis of scan field SF.
- Resonance scanners are described by way of example in Pawley, Handbook of Biological Confocal Microscopy, Plenum Press, 1944, pages 461 ff. If the scanner is steered such that it scans a field asymmetrically to the optical axis, i.e., to the neutral position of the scanner mirror, an offset shift OF of the selected region ROI will be obtained in connection with a zoom effect. As a result of the already mention effect of scanner 18 to de-scan and as a result of passing through zoom optics 41 a second time, the selection of region of interest ROI in the detection beam path is again picked up in the direction toward the detector. Thus any desired selection within scan field SF can be selected as region ROI. In addition, images can be made for various selections of range ROI, and they can then be merged into a high resolution image.
- an embodiment form is advantageous which provides in a pupil of the beam path between main color splitter 17 and sample 23 an Abbe-König prism that as is known results in a rotation of the image field. The latter is also picked up again in the direction of the detector.
- FIG. 3 shows a further possible construction for a laser scanning microscope 1 in which a Nipkow disk approach is realized.
- Light-source module 2 which is depicted in FIG. 3 in greatly simplified form, illuminates a Nipkow disk 64 , as it is described by way of example in U.S. Pat. No. 6,028,306, WO 88 079695, or DE 2360197 A1, via a minilens array 65 through main color splitter 17 .
- the pinholes of the Nipkow disk which are illuminated via minilens array 65 are imaged in the sample situated in microscope module 4 .
- zoom optics 41 are again provided.
- Nipkow scanner in contrast to the construction of FIG. 1 , illumination takes place in the passage through main color splitter 17 and the beam to be detected is reflected out.
- detector 28 in contrast to FIG. 2 detector 28 is now configured for spatial resolution so that the multiple-point illumination achieved with Nipkow disk 64 is also scanned correspondingly parallel.
- suitably fixed optics 63 with positive refracting power are arranged between Nipkow disk 64 and zoom optics 41 which convert the beam exiting in divergent manner through the pinholes of Nipkow disk 64 into suitable bundle diameter.
- Main color splitter 17 for the Nipkow configuration of FIG. 3 is a classic dichroitic beam splitter, i.e., not the beam splitter mentioned above with slit-shaped or point-shaped reflecting region.
- Zoom optics 41 correspond to the construction explained above, with scanner 18 , of course, being made superfluous by Nipkow disk 64 . It can nevertheless be provided if one wishes to make the selection explained with the aid of FIG. 2 of a region ROI. The same applies to the Abbe-König prism.
- FIG. 4 An alternative approach with multiple-point scanning is shown schematically in FIG. 4 in which several light sources beam obliquely into the scanner pupil.
- zoom optics 41 for imaging between main color splitter 17 and scanner 18 , a zoom function can be realized as depicted in FIG. 2 .
- FIG. 2 Through simultaneous beaming of light bundles at various angles in a plane conjugated to the pupil, light spots are generated in a plane conjugated to the objective lens plane which simultaneously are brought by scanner 18 over a subregion of the entire object field.
- the image formation takes place through evaluation of all subimages on a spatially resolving matrix detector 28 .
- Another possible embodiment form is multiple point scanning as described in U.S. Pat. No. 6,028,306, the disclosures of which are incorporated here in full.
- a spatially resolving detector 28 is provided. The sample is then illuminated through a multiple-point light source which is realized through a beam expander with downstream microlens array which illuminates a multiple aperture plate such that a multiple-point light source is thereby realized.
- FIG. 5 shows a light source LQ 2 which is arranged behind a grid G.
- Light source LQ 2 can be united via a splitter T with a light source LQ 1 for excitation of fluorescence. Both light sources are imaged through cylinder optics ZL as a line on the sample. LQ 1 generates a homogenous line on/in the sample PR. As a result of the effect of grid G, LQ 2 generates a periodically modulated line.
- a main color splitter MDB separates the illumination from the detection.
- the MDB can be configured as a dichroitic color splitter or as a strip mirror corresponding to DE102575237. In the latter case, the MDB must be arranged in the vicinity of a pupil plane of the microscope arrangement. For the mirroring in of LQ 1 and of the zero th order of LQ 2 , it has a centrally arranged strip mirror (along the y-axis), and for LQ 2 it has two strip mirrors arranged decentrally along the y axis corresponding to the grid frequency.
- a scanner P 2 serves to move the illumination line over sample PR. Also arranged are scanning optics SO, tubular lens TL for transfer of an intermediate image ZB onto the objective pupil P 3 , objective lens O in same beam path as well as pinhole optics PO, filter F, and detector DE or slit diaphragm SB in the detector beam path.
- LQ 1 and LQ 2 are connected to a control unit for synchronization of the sample illumination with LQ 1 and LQ 2 .
- FIG. 6 depicts how an interference field of the ⁇ 1 st , 0 th , or 1 st order is formed at an amplitude grid G in transmission during irradiation with laser light. If these interference-capable fields are imaged to a sample, by way of example, in a line-shape, a Talbot structure (literature: Talbot effect) arises in the Z direction. The Talbot effect occurs upon the bending of coherent light at a planar periodic structure of period d. At distances of:
- the depth resolution of the objective lens is computed from:
- ⁇ z ⁇ a 2 2 ⁇ ⁇ , with a being the lateral resolution of the objective lens.
- the grid constant of grid G is selected such that a periodic structure in the sample results with
- the distance between the Talbot planes is equal to the depth resolution of the microscope objective lens.
- LQ 2 in combination with the grid advantageously serves to suppress fluorescent processes (Lit.: S. W. Hell and J. Wichmann, Opt. Lett. 19, 780; 1994).
- Depopulation mechanisms can by way of example be the stimulated emission (Lit.: T. A. Klar, M. Dyba, and S. W. Hell; Appl. Phys. Let. Vol 78, No.: 4, 393, 2001), the depopulation of the ground state or the purposeful switching of dyes into various emission/absorption conditions.
- the beam from LQ 1 serves to excite fluorescence,
- a beam line of LQ 1 is presented in X-Z direction which illuminates the sample homogenously in the direction of the arrow along the X axis.
- the depth resolution of the objective lens preferably is set identical to the distance between the Talbot planes.
- the fluorescence activity of the dye molecules is suppressed in the region of the black areas (grid distribution) through illumination patterns in beam (from LQ 2 ) generated by means of a grid.
- LQ 1 and LQ 2 are advantageously pulsed for this purpose.
- the dye With a pulse from LQ 1 , the dye is first excited. Before the life of the fluorescence is over (in the nanoseconds range), the de-excitation of the fluorescence molecules by the light distribution of LQ 2 takes place. After this, detection of the fluorescence photons takes place through spontaneous emission of the remaining excited fluorescence molecules. Following this, a new excitation can be homogenously effected in a new cycle with a pulse of LQ 1 .
- the excitation of the fluorescence molecules takes place in the regions previously not irradiated as a result of the light distribution of LQ 1 .
- the fluorescence photons are detected as a result of spontaneous emission in the regions previously not irradiated.
- the dye Upon the switching of the dye properties with the illumination structure of LQ 2 , the dye is illuminated until all dye molecules in the region of the illumination structure of LQ 2 are switched “dark.” Following this in the period of time in which the dye is present with these altered properties, the fluorescence molecules in the regions not previously radiated are excited through the light distribution of LQ 1 , and the fluorescence photons generated through spontaneous emission are detected.
- the depth resolution of the objective lens can in addition be reduced to a region smaller than d (distance between the Talbot levels).
- SPEM method according to the state of the art can be utilized (Lit.: Saturated patterned excitation microscopy, J. Opt. Soc. Am. A, Vol 19, No. 8, 2002).
- a simultaneous structuring in axial and lateral direction takes place.
- the simultaneous structuring in lateral and axial direction takes place through the interferometric superimposition of 3 waves ( ⁇ 1, 0, +1) which are planar in at least one axis.
- the generation of the 3 degrees can take place in various manners, by way of example through radiation of an amplitude grid with a planar wave.
- special beam splitter arrangements can be utilized (Lit.: High efficiency beam splitter for multifocal multiphoton microscopy, J. of. Microscopy, Vol. 201, Pt3, 2001, page 1), with then only 3 degrees are generated or used.
- the described invention represents a significant expansion of the application possibilities of fast confocal laser scanning microscopes.
- the significance of such a further development can be deduced with the aid of the standard literature of cellular biology and the rapid cellular and subcellular processes described there and the utilized investigation methods with a large number of dyes.
- the invention is particularly significant for the following processes and events:
- the described invention is suitable among other things for the investigation of development processes which are distinguished above all by dynamic processes in the range of tenths of a second up to hours.
- Exemplary applications on the level of associations of cells and of entire organisms are described here by way of example:
- the described invention is excellently suited for investigation of intercellular transport events since in such investigations quite small motile structures, for example proteins, with high speed (for the most part in the range of hundredths of a second) must be represented.
- applications such as FRAP and ROI bleaching are also often utilized. Examples of such studies are described here by way of example:
- Umenishi, F. et al. describes in 2000 in Biophys J., 78:1024-1035 an analysis of the spatial motility of aquaporin in GFP transfected culture cells. For this purpose, points in the cell membranes were intentionally locally bleached and the diffusion of the fluorescence in the vicinity was analyzed.
- the described invention is particularly suited for the representation of molecular and other subcellular interactions.
- very small structures with high speed in the range of hundredths of a second
- indirect techniques such as FRET with ROI bleaching also must be used. Exemplary applications are described here:
- the described invention is outstandingly suited for the investigation of for the most part extremely fast signal transmission events. These for the most part neurophysiologic events place the highest of requirements for temporal resolution since the activities mediated through ions take place in the range of hundredths of a second to smaller than a thousandth of a second. Exemplary applications of investigations in the muscular or nerve system are described below:
Landscapes
- Physics & Mathematics (AREA)
- Chemical & Material Sciences (AREA)
- Analytical Chemistry (AREA)
- General Physics & Mathematics (AREA)
- Optics & Photonics (AREA)
- Health & Medical Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biochemistry (AREA)
- General Health & Medical Sciences (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Microscoopes, Condenser (AREA)
- Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)
Abstract
Description
with a being the lateral resolution of the objective lens. Preferably the grid constant of grid G is selected such that a periodic structure in the sample results with
In this case, the distance between the Talbot planes is equal to the depth resolution of the microscope objective lens.
-
- Abdul-Karim, M. A. et al. describe in 2003 in Microvasc. Res., 66:113-125 a long-term analysis of blood vessel changes in a living animal with fluorescence images being taken at intervals over several days. The 3D records were evaluated with adaptive algorithms in order to represent the movement trajectories schematically.
- Soll, D. R. et al. describe in 2003 in Scientific World Journ. 3:827-841 a software-based analysis of movement of microscopic data of nuclei and pseudopods of living cells in all three spatial dimensions.
- Grossmann, R. et al. describe in 2002 in Glia, 37:229-240 a 3D analysis of the movements of microglia cells of rats with the data being captured over a period of up to 10 hours. Simultaneously rapid reactions of the glia also occur following traumatic damage so that a high data rate and corresponding data volumes occur.
-
- Analysis of living cells in a 3D environment whose neighboring cells react sensitively to laser illumination and which must be protected from the illumination of the 3D ROI;
- Analysis of living cells in a 3D environment with markings which are to be intentionally bleached through laser illumination, for example FRET experiments;
- Analysis of living cells in a 3D environment with markings which are to be intentionally bleached through laser illumination and simultaneously also observations are to be made outside of the ROI, for example FRAP and FLIP experiments in 3D;
- Targeted analysis of living cells in a 3D environment with markings and pharmaceuticals which demonstrate manipulation-caused changes as a result of laser illumination, for example activation of transmitters in 3D;
- Targeted analysis of living cells in a 3D environment with markings which demonstrate manipulation-caused color changes as a result of laser illumination, for example paGFP, Kaede;
- Targeted analysis of living cells in a 3D environment with very weak markings which require for example an optimal balance of confocality and detection sensitivity;
- Living cells in a 3D tissue association with varying multiple markings, for example CFP, GFP, YFP, DsRed, HcRed, and the like;
- Living cells in a 3D tissue association with markings which demonstrate function-dependent color changes, for example Ca+ markers
- Living cells in a 3D tissue association with markings which demonstrate development-caused color changes, for example transgenic animals with GFP
- Living cells in a 3D tissue association with markings which demonstrate manipulation-caused color changes as a result of laser illumination, for example paGFP, Kaede;
- Living cells in a 3D tissue association with very weak markings which require a restriction of confocality in favor of detection sensitivity;
- The last mentioned point in combination with the preceding ones.
Claims (29)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/973,130 USRE43702E1 (en) | 2004-07-16 | 2010-12-20 | Microscope with heightened resolution and linear scanning |
Applications Claiming Priority (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102004034996 | 2004-07-16 | ||
DE102004034962A DE102004034962A1 (en) | 2004-07-16 | 2004-07-16 | Microscope with increased resolution |
DE102004034996A DE102004034996A1 (en) | 2004-07-16 | 2004-07-16 | Scanning microscope with linear scan |
DE102004034962 | 2004-07-16 | ||
US10/967,343 US20060012875A1 (en) | 2004-07-16 | 2004-10-19 | Microscope with increased resolution |
US10/967,348 US20060012869A1 (en) | 2004-07-16 | 2004-10-19 | Light grid microscope with linear scanning |
US11/698,279 US7468834B2 (en) | 2004-07-16 | 2007-01-26 | Microscope with heightened resolution and linear scanning |
US12/973,130 USRE43702E1 (en) | 2004-07-16 | 2010-12-20 | Microscope with heightened resolution and linear scanning |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/698,279 Reissue US7468834B2 (en) | 2004-07-16 | 2007-01-26 | Microscope with heightened resolution and linear scanning |
Publications (1)
Publication Number | Publication Date |
---|---|
USRE43702E1 true USRE43702E1 (en) | 2012-10-02 |
Family
ID=34854187
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/967,348 Abandoned US20060012869A1 (en) | 2004-07-16 | 2004-10-19 | Light grid microscope with linear scanning |
US12/973,130 Active USRE43702E1 (en) | 2004-07-16 | 2010-12-20 | Microscope with heightened resolution and linear scanning |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/967,348 Abandoned US20060012869A1 (en) | 2004-07-16 | 2004-10-19 | Light grid microscope with linear scanning |
Country Status (5)
Country | Link |
---|---|
US (2) | US20060012869A1 (en) |
EP (1) | EP1617260B1 (en) |
JP (1) | JP4934772B2 (en) |
DE (1) | DE102004034996A1 (en) |
GB (1) | GB2416446A (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20210372928A1 (en) * | 2018-12-17 | 2021-12-02 | Lumicks Dsm Holding B.V. | Microscopy method and system |
Families Citing this family (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20100049055A1 (en) * | 2005-05-31 | 2010-02-25 | W.O.M. World Of Medicine Ag | Method and apparatus for visual characterization of tissue |
DE102006009831B4 (en) * | 2006-03-01 | 2013-07-04 | Leica Microsystems Cms Gmbh | Method and microscope for spatially high-resolution examination of samples |
US7679741B2 (en) | 2006-03-01 | 2010-03-16 | Leica Microsystems Cms Gmbh | Method and microscope for high spatial resolution examination of samples |
JP5084183B2 (en) * | 2006-06-13 | 2012-11-28 | オリンパス株式会社 | Epi-illumination optical system for microscope |
DE102006047912A1 (en) * | 2006-10-06 | 2008-04-10 | Carl Zeiss Microimaging Gmbh | Method and device for parallelized microscopic imaging |
DE102007015063B4 (en) * | 2007-03-29 | 2019-10-17 | Carl Zeiss Microscopy Gmbh | Optical arrangement for generating a light sheet |
USRE45575E1 (en) | 2007-03-29 | 2015-06-23 | Carl Zeiss Microscopy Gmbh | Optical arrangement for the production of a light-sheet |
WO2017094184A1 (en) * | 2015-12-04 | 2017-06-08 | オリンパス株式会社 | Scanning microscope and microscope image acquisition method |
CN109425597A (en) * | 2017-09-04 | 2019-03-05 | 中国科学院上海光学精密机械研究所 | The device and method of Sweat latent fingerprint detection on a kind of large format sample |
US11921045B2 (en) * | 2018-07-09 | 2024-03-05 | National University Corporation Kobe University | Holographic three-dimensional multi-spot light stimulation device and method |
CN115702777A (en) * | 2021-08-13 | 2023-02-17 | 深圳先进技术研究院 | Multifunctional two-photon microscopic imaging system |
Citations (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2360197A1 (en) | 1973-12-03 | 1975-06-05 | Ibm Deutschland | PROCESS FOR INCREASING THE DEPTH OF FOCUS AND / OR THE RESOLUTION OF LIGHT MICROSCOPES |
WO1988007695A1 (en) | 1987-03-27 | 1988-10-06 | The Board Of Trustees Of The Leland Stanford Junio | Scanning confocal optical microscope |
US5022743A (en) | 1987-03-27 | 1991-06-11 | The Board Of Trustees Of The Leland Stanford Junior University | Scanning confocal optical microscope |
DE19702753A1 (en) | 1997-01-27 | 1998-07-30 | Zeiss Carl Jena Gmbh | System for coupling radiation, preferably laser beam, in scanning head |
US5866911A (en) | 1994-07-15 | 1999-02-02 | Baer; Stephen C. | Method and apparatus for improving resolution in scanned optical system |
US6028306A (en) | 1997-05-14 | 2000-02-22 | Olympus Optical Co., Ltd. | Scanning microscope |
US6028360A (en) | 1997-06-30 | 2000-02-22 | Hitachi, Ltd. | Semiconductor integrated circuit device in which a conductive film is formed over a trap film which in turn is formed over a titanium film |
US6167173A (en) | 1997-01-27 | 2000-12-26 | Carl Zeiss Jena Gmbh | Laser scanning microscope |
DE10257237A1 (en) | 2001-12-10 | 2003-06-18 | Zeiss Carl Jena Gmbh | Optical system for microscopy comprises focussing the illuminating light on the sample at the plane between it and the eye pupil, with separation of the emitted detection light on or near the same plane |
US20030132394A1 (en) | 2001-04-07 | 2003-07-17 | Carl Zeiss Jena Gmbh | Method and arrangement for the deep resolved optical recording or a sample |
US20040047034A1 (en) | 2002-09-06 | 2004-03-11 | Ulrich Sander | Safety illumination system for surgical microscopes |
US20040051976A1 (en) | 2002-08-29 | 2004-03-18 | Accretech (Israel) Ltd | Confocal microscope with diffractively formed virtual pinhole array |
US20040145752A1 (en) | 2003-01-24 | 2004-07-29 | David Angeley | Grating sensor |
JP2005147968A (en) | 2003-11-19 | 2005-06-09 | Shimadzu Corp | Optical microscope measuring device |
US6947127B2 (en) | 2001-12-10 | 2005-09-20 | Carl Zeiss Jena Gmbh | Arrangement for the optical capture of excited and/or back scattered light beam in a sample |
US20050241653A1 (en) | 2004-04-20 | 2005-11-03 | Wavetec Vision Systems, Inc. | Integrated surgical microscope and wavefront sensor |
US7009763B1 (en) | 1998-12-22 | 2006-03-07 | Carl Zeiss Jena Gmbh | Arrangement for separating excitation light and emission light in a microscope |
Family Cites Families (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP4545337B2 (en) * | 2001-03-23 | 2010-09-15 | オリンパス株式会社 | microscope |
EP1248132B1 (en) * | 2001-04-07 | 2010-12-29 | Carl Zeiss MicroImaging GmbH | Method and arrangement for depth resolving optical detection of a probe |
DE10155002A1 (en) * | 2001-11-08 | 2003-05-22 | Zeiss Carl Jena Gmbh | Depth-resolved optical imaging method for use in biological scanning microscopy, uses phase or frequency modulation of the imaging light |
-
2004
- 2004-07-16 DE DE102004034996A patent/DE102004034996A1/en not_active Ceased
- 2004-10-01 EP EP20040023505 patent/EP1617260B1/en not_active Not-in-force
- 2004-10-19 US US10/967,348 patent/US20060012869A1/en not_active Abandoned
-
2005
- 2005-06-17 GB GB0512344A patent/GB2416446A/en not_active Withdrawn
- 2005-06-24 JP JP2005185788A patent/JP4934772B2/en not_active Expired - Fee Related
-
2010
- 2010-12-20 US US12/973,130 patent/USRE43702E1/en active Active
Patent Citations (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2360197A1 (en) | 1973-12-03 | 1975-06-05 | Ibm Deutschland | PROCESS FOR INCREASING THE DEPTH OF FOCUS AND / OR THE RESOLUTION OF LIGHT MICROSCOPES |
WO1988007695A1 (en) | 1987-03-27 | 1988-10-06 | The Board Of Trustees Of The Leland Stanford Junio | Scanning confocal optical microscope |
US5022743A (en) | 1987-03-27 | 1991-06-11 | The Board Of Trustees Of The Leland Stanford Junior University | Scanning confocal optical microscope |
US5866911A (en) | 1994-07-15 | 1999-02-02 | Baer; Stephen C. | Method and apparatus for improving resolution in scanned optical system |
DE19702753A1 (en) | 1997-01-27 | 1998-07-30 | Zeiss Carl Jena Gmbh | System for coupling radiation, preferably laser beam, in scanning head |
US6167173A (en) | 1997-01-27 | 2000-12-26 | Carl Zeiss Jena Gmbh | Laser scanning microscope |
US6028306A (en) | 1997-05-14 | 2000-02-22 | Olympus Optical Co., Ltd. | Scanning microscope |
US6028360A (en) | 1997-06-30 | 2000-02-22 | Hitachi, Ltd. | Semiconductor integrated circuit device in which a conductive film is formed over a trap film which in turn is formed over a titanium film |
US7009763B1 (en) | 1998-12-22 | 2006-03-07 | Carl Zeiss Jena Gmbh | Arrangement for separating excitation light and emission light in a microscope |
US20030132394A1 (en) | 2001-04-07 | 2003-07-17 | Carl Zeiss Jena Gmbh | Method and arrangement for the deep resolved optical recording or a sample |
DE10257237A1 (en) | 2001-12-10 | 2003-06-18 | Zeiss Carl Jena Gmbh | Optical system for microscopy comprises focussing the illuminating light on the sample at the plane between it and the eye pupil, with separation of the emitted detection light on or near the same plane |
US6947127B2 (en) | 2001-12-10 | 2005-09-20 | Carl Zeiss Jena Gmbh | Arrangement for the optical capture of excited and/or back scattered light beam in a sample |
US20040051976A1 (en) | 2002-08-29 | 2004-03-18 | Accretech (Israel) Ltd | Confocal microscope with diffractively formed virtual pinhole array |
US20040047034A1 (en) | 2002-09-06 | 2004-03-11 | Ulrich Sander | Safety illumination system for surgical microscopes |
US20040145752A1 (en) | 2003-01-24 | 2004-07-29 | David Angeley | Grating sensor |
JP2005147968A (en) | 2003-11-19 | 2005-06-09 | Shimadzu Corp | Optical microscope measuring device |
US20050241653A1 (en) | 2004-04-20 | 2005-11-03 | Wavetec Vision Systems, Inc. | Integrated surgical microscope and wavefront sensor |
Non-Patent Citations (23)
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20210372928A1 (en) * | 2018-12-17 | 2021-12-02 | Lumicks Dsm Holding B.V. | Microscopy method and system |
Also Published As
Publication number | Publication date |
---|---|
JP2006030989A (en) | 2006-02-02 |
EP1617260A1 (en) | 2006-01-18 |
EP1617260B1 (en) | 2014-03-05 |
GB2416446A (en) | 2006-01-25 |
DE102004034996A1 (en) | 2006-02-02 |
US20060012869A1 (en) | 2006-01-19 |
JP4934772B2 (en) | 2012-05-16 |
GB0512344D0 (en) | 2005-07-27 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7468834B2 (en) | Microscope with heightened resolution and linear scanning | |
USRE43702E1 (en) | Microscope with heightened resolution and linear scanning | |
US20080048105A1 (en) | Procedure for the optical acquisition of objects by means of a light raster microscope | |
US7888628B2 (en) | Optical zoom system for a light scanning microscope | |
US20090046360A1 (en) | Raster scanning light microscope with line pattern scanning and applications | |
US20080285123A1 (en) | Raster scanning light microscope | |
GB2416443A (en) | Laser scanning microscope with linear illumination and confocal diaphragm | |
GB2416263A (en) | Laser scanning microscope with linear illumination and confocal slit diaphragm | |
US7369305B2 (en) | Optical zoom system for a light scanning electron microscope | |
GB2416444A (en) | Laser scanning microscope with variably split illumination | |
US20080149818A1 (en) | Procedure for the optical acquisition of objects by means of a light raster microscope with line by line scanning | |
US7235777B2 (en) | Light scanning microscope and use | |
GB2416441A (en) | Laser scanning microscope with adjustable scanning steps | |
GB2416452A (en) | Zoom optics for a confocal laser scanning microscope | |
GB2416261A (en) | Laser scanning microscope with parallel illumination and simultaneous, locally resolved detection | |
JP2006053542A (en) | Line scanning system optical scanning microscope and usage of the same | |
US20060012870A1 (en) | Light scanning microscope with line-by-line scanning and use | |
JP2006030997A (en) | Optical scanning microscope with movable perforated disk, and use thereof | |
GB2416440A (en) | Laser scanning microscope with parallel illumination via distributed point like light sources | |
US7304280B2 (en) | Laser line scanning microscope and method of use | |
US7369307B2 (en) | Light raster microscope and its use |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: CARL ZEISS JENA GMBH, GERMANY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:WOLLESCHENSKY, RALF;REEL/FRAME:028797/0365 Effective date: 20050204 Owner name: CARL ZEISS MICROIMAGING GMBH, GERMANY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CARL ZEISS JENA GMBH;REEL/FRAME:028797/0465 Effective date: 20080923 |
|
FEPP | Fee payment procedure |
Free format text: PAYOR NUMBER ASSIGNED (ORIGINAL EVENT CODE: ASPN); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY |
|
AS | Assignment |
Owner name: CARL ZEISS MICROSCOPY GMBH, GERMANY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CARL ZEISS MICROIMAGING GMBH;REEL/FRAME:030110/0441 Effective date: 20130227 |
|
AS | Assignment |
Owner name: CARL ZEISS MICROSCOPY GMBH, GERMANY Free format text: CHANGE OF NAME;ASSIGNOR:CARL ZEISS MICROIMAGING GMBH;REEL/FRAME:030610/0269 Effective date: 20120403 |
|
FPAY | Fee payment |
Year of fee payment: 8 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 12TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1553); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 12 |