EP1664886A1

EP1664886A1 - Multiphoton fluorescence microscope with plane array detector

Info

Publication number: EP1664886A1
Application number: EP04765183A
Authority: EP
Inventors: Dan Davidovici
Original assignee: Carl Zeiss Jena GmbH
Current assignee: Jenoptik AG
Priority date: 2003-09-18
Filing date: 2004-09-14
Publication date: 2006-06-07
Also published as: WO2005029148A1; DE10343276A1; US20060245021A1; JP2007506123A

Abstract

A multiphoton fluorescence microscope (M) is disclosed, comprising an excitation beam path, with a lens (2) which collects the excitation beam (1) at a focal point (4) in the sample (5), a scan device, which adjusts the focal point (4) at least one-dimensionally, and a detector device which records fluorescence radiation stimulated in the sample by multiphoton excitation, whereby the detector device comprises a plane array detector (9), located on the opposite side of the sample (5) to the lens (2).

Description

MULTI-PHOTON FLUORESCENCE MICROSCOPE WITH SURFACE DETECTOR

The invention relates to a multi-photon luminescence microscope with an excitation beam path that has an objective that bundles excitation radiation in a focal point in the sample, a scanning device that adjusts the focal point at least one-dimensionally, and a detector device that in the sample luminescent radiation stimulated by multi-photon excitation. The invention further relates to a method for multi-photon luminescence microscopy, in which excitation radiation is concentrated in a focus point lying in a sample, thereby stimulating luminescence radiation in the sample by multi-phone excitation, the focus point is adjusted for scanning the sample and the Luminescence radiation is detected.

In conventional luminescence microscopy, fluorophores or

Self-luminescent effects stimulated in a sample. A bundled excitation radiation, usually laser radiation, which is matched to maximum luminescence, is usually used for this purpose. The excitation takes place in the focus area, luminescence also being stimulated in the incident or emerging light cone of the focused beam. For image generation, the luminescence radiation is recorded by confocal detection only from the area of the focus of the excitation radiation. An image is created by scanning a sample.

In multi-photon luminescence microscopy, the excitation radiation is selected spectrally in such a way that at least two photons are required to effect an excitation. Since the probability of excitation is thus greatly reduced, effective excitation can only take place at a very high flux density, which is only given exactly in the focus of the bundled excitation radiation. Therefore, emission of luminescence or fluorescence radiation is only stimulated at the focal point. The confocal detection required in conventional luminescence microscopy can be dispensed with, since it is not necessary to emit lurninescence radiation that was emitted outside the focus of the excitation radiation. Multi-photoneh luminescence microscopy works with it without confocal stray light suppression during detection. The detectors used are called direct detectors. In this regard, reference is made to the microscopes from BIO-RAD Microscience, USA. The document http: Wmicroscopy.bio- rad.com/faqs/multophotone/faqs2.htm available on the Internet proposes as a direct detector a photomultiplier unit that is also customary for confocal microscopy, which is coupled into the excitation beam path via a chromatic beam splitter and absorbs fluorescent radiation, which runs in the opposite direction to the radiation of the excitation radiation. A corresponding converging lens is connected upstream of the photomultiplier tube used in the unit, which together with an objective lens present in the excitation beam path completely images the sample field onto the relatively small window of the highly sensitive photomultiplier tube. Since this must be done for the entire scanning of the sample, a certain amount of optical effort is inevitable, especially since the objective lens used for imaging is also part of the focusing of the laser beam that excites the multi-photon fluorescence. W. Denk et al., "Twö-photon melecular excitation in laser scanning microscopy" in "Handbook of Biological Confoeal Microscopy", Plenum Press, New York, 1995, disclosed using a photomultiplier tube in transmitted light mode. DE 198 01 139, which was submitted in 1998, also provides for this, in addition to which a condenser is used, as is used in BIO-RAD in reflected light mode.

The invention has for its object to develop a multi-photon luminescence microscope of the type mentioned and a corresponding method for multi-photon luminescence microscopy so that radiation detection is possible with reduced effort.

This object is achieved with a microscope of the type mentioned at the outset, in which the detector device has an area detector which is located on the side of the sample opposite the objective. The object is further achieved by a method of the type mentioned at the outset, in which the luminescent radiation is areally detected on the side opposite the radiation of the excitation radiation.

According to the invention, a so-called “direct” detector is used, which is now designed as an area detector that is located on the side of the sample opposite the objective. Area detector is understood to mean any detector whose detector area is larger than the light path to the sample in The arrangement of such an area detector in the transmit mode makes it possible, on the one hand, to dispense with chromatic beam splitters which reduce the intensity, and on the other hand, the area detector can be arranged at an extremely short distance from the sample, so that it has a large clearing angle with respect to the Covers the sample of lurninescence radiation Area detector used in transmisive operation receives much more luminescence radiation intensity and thus achieves a better signal / noise ratio; this is particularly so because there are no losses through intermediary optics, such as imaging optics or dichroic beam splitters, which are also used for irradiation of the excitation radiation. The detection of the lurninescence radiation no longer has to take place through the objective of the excitation beam path.

In order to cover the largest possible solid angle, it is advantageous for the area detector to be at a distance from the focal point that is very much smaller than the extent of the area detector, for example only one tenth of it.

In the case of many detectors with a large detection area, it is advantageous to let the radiation fall as perpendicularly as possible to the flat detection area, since the detection probability is then maximum. For signal homogenization, it is therefore preferred to arrange an optical element between the surface detector and the sample, which directs lurninescence radiation which arises in the sample onto the surface detector. In particular, it is not used to introduce the excitation radiation. In a particularly simple embodiment, the optical element can be designed as a grating, preferably as a holographic grating.

In a construction that is particularly easy to implement, such an optical element can also be attached directly to the underside of a sample carrier that is used in the luminescence microscope.

With luminescence microscopy it is possible to identify biological samples on the basis of their own luminescence spectrum. This procedure is also possible in the luminescence microscope according to the invention if a spatially resolving surface detector is used and a spectral analyzer is connected between the surface detector and the sample, which spectrally decomposes the radiation emanating from the sample. In a very simple design, the grating already mentioned is arranged between the sample and the area detector for spectral decomposition. For this purpose, the grating or the area detector is coupled with a suitable mechanism which carries out a one- or two-dimensional transverse displacement (in relation to the areal formation of the specimen to be examined). Moving the grating or the surface detector causes a shift in the interference pattern, which is dependent on the intrinsic luminescence spectrum, and thus permits sample identification. Alternatively or additionally, the signal / noise ratio can be increased if a known spectral distribution is sought. The invention is explained in more detail below by way of example with reference to the drawings. In the drawings:

Fig. 1 is a schematic representation of a section of a microscope for multi-photon fluorescence microscopy and

2 shows a schematic representation of the laser beam which excites a multi-photon fluorescence.

In Fig. 1, a microscope M is shown schematically, which allows multi-photon fluorescence or luminescence microscopy. 1 shows only the area of the microscope in which the sample is located.

The microscope M has a beam source (not shown) which emits a laser beam 1 with a wavelength around 700 nm. The laser beam 1 passes through an objective 2, which emits a focused beam 3. The focus 4 lies in a sample 5, which is located under the lens 2 behind a cover glass 6 on a sample holder 7.

The laser beam 1 focused in this way in the sample 5, as shown in FIG. 2, causes a multi-photon excitation in the sample 5. Either an inherent fluorescence of the biological material of the sample 5 or a fluorescence specifically provided in the sample 5 can be provided Fluorophores are stimulated. The laser beam 1, which is focused in a beam waist T by the objective 2, which is only shown schematically in FIG. 2, only reaches a beam density in the area of the focus 4, which is sufficient to excite multi-photon fluorescence. No more photon fluorescence can be excited with sufficient probability outside the beam waist T. Therefore, fluorescence radiation only arises in the area of focus 4. No fluorescence occurs at other points in the focused beam 3.

With microscope M it can therefore be assumed that fluorescence radiation originates exclusively from focus 4. A spatially resolving detection of the fluorescent radiation is therefore not necessary. In order to be able to absorb the fluorescence radiation emitted homogeneously in the focus 4 as completely as possible, a grating 8 is arranged under the sample carrier 7, which redirects radiation emanating within a beam cone K to a CCD sensor 9 in such a way that the radiation falls as perpendicularly as possible onto the sensor 9 ,

The optional grating is located at a very small distance d below the focus 4, so that in combination with the comparatively large extent of the in FIG. 1 only as The sectional view shown sensor 9 covers a very large solid angle based on the focus 4.

Since the representation in Fig. 1 with respect to the thicknesses of the sample 5, the sample carrier 7 and the grid 8, in particular. With regard to the distance d, which is not significant, but is greatly enlarged, the unit comprising the grating 8 and the sensor 9, which embodies the area detector, collects almost all fluorescence radiation emitted in a half space. This greatly improves the signal-to-noise ratio.

The CCD sensor 9, which in the present example is designed as a back-illuminated CCD sensor, supplies the corresponding image information to a control device 10. This carries out the signal evaluation.

Various approaches can be used to mask out the excitation radiation 1 which is also directed onto the detector unit. On the one hand, a sensor 9 can be used which is not sensitive to the excitation radiation. On the other hand, with the

Using a pulsed excitation radiation, the reading of the sensor 9 can be limited to periods in which no excitation radiation 1 is emitted. It is also possible to hide the relatively small area of the area detector in which excitation radiation falls on the sensor 9. Either a spatially resolving detector can be used for this, which is not read out in the area concerned, or sensor 9 becomes a suitable one

(if necessary adjustable) aperture device upstream. Another possibility is the use of a suitable filter or dichroic reflector that the

Keeps excitation radiation away from the detector. These options for suppressing the excitation radiation by temporally or locally blanking out can of course be used alone or in any combination.

In the present exemplary embodiment, a filter for excitation radiation is attached to the underside of the sample carrier 7 and / or to the grating 8. It is an infrared cut filter that blocks at 700 nm.

A further improvement in the signal-to-noise ratio or further information acquisition is possible if the grating 8 spectrally decomposes the fluorescent radiation entering the beam cone K. For this purpose, the control device 10 reads out the (location-detecting) sensor 9 in a suitable manner and identifies a sample 5 on the basis of its own fluorescence spectrum. The spectral activity of the grating 8 also opens up an additional spectral possibility of masking the excitation radiation 1, since it differs significantly from the fluorescence radiation. As a rule, the grating 8 will generate an interference pattern on the sensor 9. For spectral analysis, it is provided in one embodiment that the control device 10 effects a relative shift of the grating 8 and the sensor 9, so that the interference pattern, which indicates the spectral composition of the fluorescent radiation entering the beam cone K (optionally together with excitation radiation 1), changes. The change then enables the control unit 10 to make a statement about the spectral composition of the fluorescent radiation from the focus 4 using known algorithms.

In order to achieve the largest possible solid angle, the distance d should of course be as small as possible. In a further embodiment (not shown in FIG. 1), the grid 8 is therefore attached directly to the underside of the sample carrier 7. Without the grating 8, the distance d (now between the focus 4 and the sensor 9) should be minimized by the sensor being as close as possible to the sample carrier 7.

Claims

claims

1. Multi-photon luminescence microscope (M) with an excitation beam path, which has a lens (2) that bundles excitation radiation (1) at a focal point (4) in the sample (5), a scanning device that measures the focus point ( 4) adjusted at least one dimension and a detector device which receives lurninescence radiation stimulated in the sample by multi-photon excitation, characterized in that the detector device has an area detector (9) which is located on the side of the sample (2) opposite the objective (2) 5) is located.

2. Microscope according to claim 1, characterized in that the area detector (9) lies at a distance (d) from the focal point (4) which is small against the extent (b) of the area detector (9) by as large a solid angle ( K) to cover.

3. Microscope according to one of the above claims, characterized in that a, preferably holographic, grating (8) is arranged between the surface detector (9) and the sample (5).

4. Microscope according to claim 3, characterized in that the grating (8) is applied to the underside of a sample carrier (7).

5. Microscope according to one of the above claims, characterized by a spatially resolving surface detector (9).

6. Microscope according to claim 5, characterized by a CCD area detector (9), preferably as a back-lit CCD sensor.

7. Method for multi-photon luminescence microscopy, in which excitation radiation (1) is concentrated in a focus point (4) lying in a sample (5), thereby stimulating lurninescence radiation in the sample (5) by multi-photon excitation, the focus point (4 ) back Scanning the sample (5) is adjusted and the lurninescence radiation is detected, characterized in that the lurninescence radiation is areally detected on the side opposite the radiation of the excitation radiation.

8. The method according to claim 7, characterized in that a spectral decomposition of the lurninescence radiation takes place before the detection.