Patent Application
20230324668
The invention relates to an operating microscope according to the preamble of claim 1.
It is already known to capture so-called reflection images of organic tissue. In this case, light is guided onto tissue to be examined and light reflected by the tissue is captured in order to generate reflection images. It is also known to capture so-called fluorescence images of organic tissue. Fluorescein, for example, may be distributed as an indicator in the tissue and excited into fluorescence by light. Fluorescein is a dye which fluoresces and, in particular, is used as an indicator in ophthalmology.
Against this background, operating microscopes with which organic tissue can be examined are currently used. Operating microscopes are used by doctors in a very wide variety of medical specialisms in order to capture images of organs or organ regions during an operation and in order to make a medical diagnosis with the aid of these images.
Irrespective of the medical discipline, the depth of field of camera-based operating microscopes is constantly being criticized by surgeons.
The object of the invention is therefore to provide an operating microscope which allows the most accurate possible capture and pictorial representation of tissue structures.
The present invention achieves the aforementioned object by the features of claim 1.
The use of two simultaneously operating camera devices permits capture and representation of reflection images and further images, for example fluorescence images, at the same time. By using two camera devices, it is possible to provide two camera planes, the camera devices supplementing one another during the image capture and representation and thus being able to compensate for quality losses during the image capture. If at least one of the camera devices consists of two cameras in a stereo arrangement, a spatial impression may be optically generated for the user. The tissue can be examined and observed very comprehensively. Chronologically alternating acquisition and representation of two imaging modes, for example reflection mode and fluorescence mode, may be dispensed with because of a flickering illumination required therefor and the associated distracting effects.
According to the invention, an operating microscope is assigned a second camera plane. Besides fluorescence representation at the same time, the second camera plane also offers further possibilities of optical representation improvement, for example so-called focus stacking, increasing the resolution by intermediate sampling, noise reduction and extension of the dynamic range by different exposure of the various camera units or camera devices.
“Focus stacking” to a person skilled in the art means the concept of an increase in the depth of field which is achieved by a combination of optical photographic capture techniques and digital image editing or image processing. Thus, images having a very large depth of field may be generated.
Against this background, each camera device could have at least two individual cameras. The two preferred operating modes, namely reflection mode and fluorescence mode, each generate a three-dimensional impression for the user. In order to generate this three-dimensional impression, two detection channels per camera device are respectively used. Both detection channel pairs preferably use the same zoom optics in order to keep the structure of an optical arrangement as simple as possible.
At least one camera device or both camera devices could perform image recordings in the video mode. Thus, movements of the tissue may also be captured well. The two preferred operating modes, namely reflection mode and fluorescence mode, may be carried out on the basis of video recordings. Thus, an in-situ examination of the tissue as well as a chronologically subsequent check of the video recordings, preferably outside an operating room, may be carried out.
The further image could be configured as a fluorescence image of the object. Thus, reflection images and fluorescence images of the same object may be acquired, represented and evaluated at the same time.
Against this background, one illumination device could have a fluorescence excitation light source. Alternatively, two illumination devices could be provided, each having a fluorescence excitation light source.
To this extent, there is initially only a basic design of the operating microscope, although it may be supplemented with further light sources.
In another embodiment of the operating microscope, a light source present for the generation of reflection images could be turned off during the detection of the fluorescence. In this way, further filters are not necessary in order to stop out a wavelength range at which fluorescence takes place.
A blocking filter or else barrier filter could be provided, which is placed optically in front of the two camera devices so that a light pencil component incident on the two camera devices has to pass through the blocking filter. For a fluorescence mode, there must be a sufficiently large spectral power density at the wavelength of the excitation light of the illumination device. Spectral ranges of the excitation light, or of the excitation light reflected as reflection light, may be stopped out simultaneously for both camera pairs by the blocking filter.
The blocking filter could, for example, against this background, not transmit, or at least suppress, light with a wavelength from the wavelength range of 480 nm to 490 nm. Fluorescein is excited into fluorescence by excitation light of the wavelength 485 nm. Preferably, the excitation light may be stopped out for each wavelength individually. In the case of narrowband excitation, such as may be generated by a laser, the blocking filter may also remain in the beam path during other modes and/or be configured statically if white balancing is furthermore possible. Preferably, a filter change option is provided by design in the optical arrangement.
When the operating microscope is operating in the fluorescence mode, the wavelength range detected during a respective fluorescence must be filtered out from the spectrum of the illumination device so that excitation light reflected as reflection light, or returning excitation light, is not superimposed on the fluorescence acquisition on or by the second camera device. This is preferably achieved by a light module, which is preferably not provided in the camera device.
In the fluorescence mode, the light which impinges on the second camera device must be filtered by a suitable bandpass filter or bandwidth filter for the wavelength to be detected, in order to stop out the reflection light, incident on the second camera device, of the excitation light. This bandpass filter could preferably be capable of being switched over for different dyes, or could be capable of being moved away when other modes are active.
Against this background, a bandpass filter could be provided, which is placed optically in front of the second camera device so that a light pencil component incident on the second camera device has to pass through the bandpass filter before it impinges on the second camera device.
The bandpass filter could therefore, for example, transmit light with a wavelength from the wavelength range of 510 nm to 540 nm and not transmit, or at least suppress, the rest of the spectral range. In this way, a large proportion of the fluorescence light of fluorescein is transmitted to the second camera device and rather nonessential light is stopped out.
Against this background, an optical arrangement in which the blocking filter is not present is therefore also conceivable, specifically when the bandpass filter completely suppresses the excitation light reflected as reflection light before the second camera device and the high spectral power density at the wavelength of the excitation light can be tolerated, or corrected, during the representation of the reflection image simultaneously taking place via or by the first camera device. If a blocking filter is not present, the bandpass filter must also suppress the high spectral power density of the excitation light. The blocking filter is then preferably integrated in the bandpass filter.
At least one beam splitter, preferably a 50:50 beam splitter, onto which a first light pencil component can be guided for splitting into a second and a third light pencil component, could be arranged in the beam path between an objective over the specimen and the two camera devices. By this beam splitter, at least a part of the light which is reflected by the specimen or is emitted as fluorescence light, namely reflection light and fluorescence light, can be guided simultaneously to the two camera devices.
Against this background, the beam splitter could guide the second light pencil component in the direction of the first camera device and guide the third light pencil component, through a bandpass filter in front of the second camera device, onto the latter. Thus, in a filtered manner, light for reflection images may be guided to the first camera device and light for fluorescence images to the second camera device.
An OCT apparatus, by the sampling light of which the specimen can be examined, could also be provided in addition. Thus, besides reflection images and fluorescence images, OCT images may also be acquired in a known way.
The term optical coherence tomography, (conventionally abbreviated to OCT) refers to an image generation method. With this method, two-dimensional and three-dimensional images may be obtained from light-scattering organic tissues.
Irrespective of the medical discipline, the depth of field of camera-based operating microscopes is constantly being criticized by surgeons. Owing to the lack of the observer's capability of accommodation, the depth of field is reduced to the numerical aperture, dictated by the geometrical aperture, of the objective of the operating microscope.
Reduction of the aperture diameter in order to increase the depth of field is only limitedly possible because this is associated both with a possibly unusable brightness increase, which ultimately leads to heating of the tissue, and associated with a signal amplification so that an increase in the noise takes place, and is associated with a decrease in the MTF so that there is a lower resolution.
The abbreviation MTF refers to the so-called modulation transfer function, or contrast transfer function, which mathematically describes a comparison between the detail contrast at edges of an object and the detail contrast of its pictorial representation.
Against this background, an operating microscope of the type described here could have an image processing device which connects at least one first image, which is acquired by the first camera device, to at least one further image, which is acquired by the second camera device, the images being selected by the image processing device on the basis of a predefined sharpness quality of the images and composited to form an overall image.
The second camera device described here, namely a second camera plane, may inter alia be used to patch regions with acceptable sharpness together. In this case, the imaging plane of the second camera plane would be displaced relative to the first, for example by half the depth of field range. The final image or overall image would then be combined algorithmically from the two slice acquisitions, or images.
Static or temporal denoising algorithms for noise reduction, with which parameterizable noise can be suppressed, could additionally be used. By the synchronization of the sampling of the two camera planes or camera devices, methods which are based on time averaging could also be employed. So-called temporal oversampling may take place.
Image sensors which are sensitive for infrared light, preferably for infrared light from the wavelength range of from 1000 to 1500 nm, could be provided in the first and/or second camera device. For hyperspectral image generation, for example in the infrared range of up to 1500 nm, it could be possible to use image sensors which are sensitive in the far infrared and are used for spectral tissue 15 differentiation. Tumor detection is preferably carried out in the spectral range of 1000-1500 nm.
A resolution increase could take place by oversampling. By diagonal displacement of two sampling grids with respect to one another by one half of a 20 pixel, the resolution may be increased by about 1.4 times, i.e. root 2 times.
In the case of so-called downsampling to the display size of the image, for example HD or 4K, the shape of the MTF and therefore the sharpness of the image may be influenced.
The advantage of this technique primarily leads not to a resolution increase but to a sharper image. This is attributable to the boosting of the low spatial frequencies. Furthermore, the oversample image could be used for loss-free digital enlargement and/or zooming.
By different amplification or different illumination or different exposure of the two camera planes or camera devices, a dynamic range could be increased.
One particular feature is the balancing of the characteristic curves of the two image pairs, that is to say configuring the join in the transition region in such a way that an artefact-free HDR image is obtained.
In the drawing
Each camera device 1, 2 has at least two cameras. Each camera device 1, 2 is to this extent a camera pair. At least one camera device 1, 2 or both camera devices 1, 2 performs or perform image recordings in the video mode. The first camera device 1 is used to capture reflection images. The second camera device 2 is used to capture fluorescence images.
At least one illumination device 4a, 4b having a fluorescence excitation light source 5 is provided, or two illumination devices 4a, 4b are provided, each having a fluorescence excitation light source 5. An illumination device 4a, 4b comprises a field illumination light source 6 and/or an SCI light source 7. The abbreviation SCI stands for “Stereo Confocal Illumination”.
The illumination of the object, namely a specimen 3, in particular an organic tissue, may to this extent be carried out by means of two alternatives. According to the first alternative, a first illumination device 4a comprises as fluorescence excitation light source 5 a field illumination light source 6. The fluorescence illumination is generated by the field illumination light source 6.
According to a second alternative, a second illumination device 4b comprises as the fluorescence excitation light source 5 an SCI light source 7.
In a first embodiment of the arrangement, the SCI light source 7 is absent. This operating microscope constitutes a basic design. In another design, a physically present SCI light source 7 may be turned off during the detection of the fluorescence.
The excitation light from an illumination device 4a, 4b impinges through an objective 8 on the specimen 3 and excites the latter to emit fluorescence light since fluorescein is present in the specimen 3. At the same time, the excitation light impinging on the specimen 3 is at least partially reflected by the specimen 3 as reflection light.
Furthermore, according to a particular embodiment of the arrangement, sampling light 9 of an OCT apparatus 10 also impinges on the specimen 3 so that the latter can be examined in more detail.
The reflection light reflected onto the incident excitation light of the illumination device 4a, 4b by the specimen 3 and the fluorescence light, represented in
By the second beam splitter 13, a first light pencil component 14 is directed through zoom optics 15, for example an objective having a variable focal length, through a blocking filter 16 onto a third beam splitter 17, namely a 50:50 beam splitter. The first light pencil component 14 is split into a second light pencil component 18 and into a third light pencil component 19. The third beam splitter 17 could, in another embodiment, be configured to be dichroic.
The second light pencil component 18 impinges on the first camera device 1 in order to generate reflection images. After deflection by a mirror 20 and after passing through a bandpass filter 21, the third light pencil component 19 impinges on the second camera device 2 in order to generate fluorescence images.
In one embodiment of the arrangement, the blocking filter 16 is placed in front of both camera devices 1, 2 so that a first light pencil component 14 impinging on the camera devices 1, 2 has to pass through the blocking filter 16. The blocking filter 16 does not transmit light with a wavelength from the wavelength range of 480 nm to 490 nm.
The bandpass filter 21 is placed in front of the second camera device 2 so that a third light pencil component 19 impinging on the second camera device 2 has to pass through the bandpass filter 21. The bandpass filter 21 transmits light with a wavelength from the wavelength range of 510 nm to 540 nm and does not transmit light of the rest of the spectral range.
Arranged in the beam path between the objective 8 and the two camera devices 1, 2 in all embodiments is the third beam splitter 17, onto which the first light pencil component 14 can be guided for splitting into the second and third light pencil components 18, 19. The third beam splitter 17 guides the second light pencil component 18 in the direction of the first camera device 1 and the third light pencil component 19 through the bandpass filter 21 in front of the second camera device 2, onto the latter.
The optionally provided blocking filter 16 and the bandpass filter 21 are intended to filter out the excitation light which, in particular, could impinge as reflection light on the second camera device 2 and interfere with the detection of the actual fluorescence.
Excitation of the known indicator fluorescein by excitation light of the illumination device 4a, 4b preferably takes place at a wavelength of 485 nm. Light with this wavelength is blue. More than 80% of the fluorescence excited by this light occurs in the range of 510 to 540 nm. Depending on the width of the spectrum of the excitation light, the blocking filter 16 must therefore block the wavelengths around 485 nm with a width of about 5 nm, but transmit the rest of the visible range. This optical behavior is schematically represented at the very top in
The bandpass filter 21 is transparent for the fluorescence light to be detected with wavelengths in the range of 510 to 540 nm, and blocks the entire rest of the spectral range for which the second camera device 2 could be sensitive. This optical behavior of the bandpass filter 21 is represented in
The spectral range of 510 to 540 nm could be stopped out from the spectrum of the excitation light of the illumination device 4a, 4b. At the wavelength 485 nm, however, the required power density must be made available. This is represented at the very bottom in
In order to produce the blocking filter 16, a filter wheel having x positions could be provided in the relevant beam paths. Each adjustment position then represents an achieved fluorescence light wavelength and a basic position represents a neutral state. In order to produce the bandpass filter 21, a filter wheel having x positions could likewise be provided in the relevant beam paths in front of the second camera device 2. Each adjustment position represents an achieved fluorescence light wavelength and a basic position represents a neutral state.
Thus, each wavelength range in which fluorescence is detected could be filtered out from the excitation light, or excitation light reflected as reflection light, of the illumination device 4a, 4b.
The excitation of the fluorescence could also be carried out with a laser having a wavelength of about 488 nm. Fluorescence or a reflection image generated by the laser may be acquired. In both cases, about 1/10 000 of the incident light is recovered, that is to say a blue image has the same gray levels as a fluorescence image.
1 first camera device
2 second camera device
3 specimen
4
a first illumination device
4
b second illumination device
5 fluorescence excitation light source
6 field illumination light source of 4a
7 SCI light source of 4b
8 objective
9 sampling light
9
a light sent back by 3
10 OCT apparatus/OCT interferometer
11 returning light ray pencil
12 first beam splitter
13 second beam splitter
14 first light pencil component
15 zoom optics
16 blocking filter
17 third beam splitter
18 second light pencil component
19 third light pencil component
20 mirror
21 bandpass filter
22 first image
23 second or further image
24 overall image
25 third image
| Number | Date | Country | Kind |
|---|---|---|---|
| 10 2020 123 365.5 | Sep 2020 | DE | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2021/064745 | 6/2/2021 | WO |
