DE102020105458B4 - Medical imaging device - Google Patents

Abstract

Medical imaging device, in particular endoscopic imaging device, with at least one image capture unit (10), which has at least one image capture sensor system (12) and at least one optical filter unit (16), which has at least one spectral filter (18), which is designed as an interference filter (38), comprises, which is assigned to the image capture sensor system (12) and is arranged in front of the image capture sensor system (12) when viewed in the viewing direction (20), wherein the spectral filter (18) in a first operating state is designed to provide light according to a first spectral transmission range (22). Image capture sensor system (12) and in a second operating state is designed to transmit light according to a second spectral transmission range (24), which is at least partially different from the first spectral transmission range (22), to the image capture sensor system (12) and the image capture unit ( 10) comprises at least one bearing (40) designed as a tilting bearing, which is designed to store the spectral filter (18) so that it can be transferred from the first operating state to the second operating state and / or vice versa, and with at least one lighting unit (44), which is used for Illumination of an object to be captured by the image capture unit (10) is designed, wherein the illumination unit (44) is designed to provide at least a first illumination light according to an illumination spectrum (46) which lies at least to a large extent outside the first spectral transmission range (22). , wherein the illumination spectrum (46) corresponds at least to a large extent to an absorption spectrum (48) of a spontaneously light-emitting material of the object to be illuminated, wherein an emission spectrum (52) of a spontaneously light-emitting material illuminated by means of the lighting unit (44) is at least to a large extent in first spectral transmission range (22) and wherein the lighting unit (44) is designed to provide at least a second illumination light with an illumination spectrum (47), namely white light, which lies at least to a large extent in the second spectral transmission range (24).

Description

State of the art

The invention relates to a medical imaging device according to the preamble of claim 1, and a method for operating a medical imaging device according to the preamble of claim 19.

From the EP1327414B1 A device for the imaging diagnosis of tissue is already known, with a transmittance of an illuminating light being adjustable by means of a variable spectral filter. The US 6,110,106 A teaches the use of such a variable spectral filter to select specific wavelength ranges from light reflected from tissue. From the DE 10 2008 034 008 A1 a filter set for observing fluorescence radiation is known, the filter set having filter wheels with spectrally different observation filters.

The object of the invention is, in particular, to provide a generic device with improved properties with regard to efficiency, in particular with regard to imaging efficiency and/or installation space or component efficiency. The object is achieved according to the invention by the features of patent claim 1, while advantageous refinements and developments of the invention can be found in the subclaims.

Advantages of the invention

The invention is based on a medical imaging device, in particular an endoscopic imaging device, with at least one image capture unit, which has at least one image capture sensor system and at least one optical filter unit, which comprises at least one spectral filter, which is assigned to the image capture sensor system and is arranged in front of the image capture sensor system when viewed in the viewing direction .

It is proposed that the spectral filter is designed in at least a first operating state to transmit light according to a first spectral transmission range to the image capture sensor system and in at least a second operating state is designed to transmit light according to a second spectral transmission range, which is at least different from the first spectral transmission range is partly different to transmit to the image capture sensor system. In this way, in particular, a medical image capture device with improved efficiency can be provided. In particular, the efficiency of imaging can be improved, since in particular spectral imaging components can be distinguished by means of the first spectral transmission range and the second spectral transmission range. In addition, the installation space or component efficiency of the medical imaging device can advantageously be improved, since instead of one spectral filter per transmission range, a single spectral filter can be used, the position dependence of which relative to the image capture sensor system enables the provision of both a first spectral transmission range and a second spectral transmission range , which means that additional spectral filters and space for their arrangement can be saved as components.

The medical imaging device is set up in particular for multispectral imaging and preferably hyperspectral imaging. “Multispectral imaging” is intended to mean, in particular, imaging in which at least three spectral bands can be detected independently of one another. “Hyperspectral imaging” is intended to mean, in particular, imaging in which at least twenty spectral bands can be detected independently of each other. The present medical imaging device is particularly preferably suitable for multispectral imaging and preferably hyperspectral imaging according to a time-resolved snapshot method, in which the spectral bands are recorded with a time offset with only a single detector output. A “medical imaging device” should be understood to mean in particular a, preferably functional, component, in particular a subassembly and/or a construction and/or a functional component of a medical imaging device and/or a medical imaging system. Preferably, the medical imaging device can form the medical imaging device and/or the medical imaging system at least partially, preferably at least to a large extent and particularly preferably completely. The medical imaging device can be a microscopic, macroscopic and/or exoscopic imaging device, which, for example, acts as an imaging device, at least partially and preferably at least to a large extent, a microscope, a macroscope and/or an exoscope and/or as an imaging system. at least partially forms a microscope, a macroscope and / or an exoscope system. The medical imaging device is preferably designed as an endoscopic imaging device, which in particular is at least partially and preferably at least to a large extent an endoscope and/or forms an endoscope system. The endoscopic imaging device is in particular designed to be inserted at least partially and preferably at least to a large extent into an artificial cavity, such as a housing, and/or a natural cavity, such as a cavity in a body organ or in tissue, in order to examine it . “Trained” is intended to mean, in particular, specifically programmed, designed and/or equipped. The fact that an object is designed for a specific function should be understood in particular to mean that the object fulfills and/or carries out this specific function in at least one application and/or operating state. The expression “at least to a large extent” should be understood to mean in particular at least 55%, more preferably at least 65%, preferably at least 75%, particularly preferably at least 85% and most preferably at least 95% and advantageously completely particularly with reference to a volume and/or mass of an object.

The medical image capture device has at least a proximal section, a distal section and/or an intermediate section. The distal section is designed in particular to be inserted into a cavity to be examined in an operating state. The proximal section is designed in particular to be arranged outside the cavity to be examined in an operating state. “Distal” should be understood to mean facing a patient and/or away from an operator, particularly when operating. In particular, proximal is the opposite of distal. “Proximal” should be understood to mean facing away from a patient and/or facing an operator, particularly when operating. The medical image capture device in particular has at least one, preferably flexible, shaft. The shaft is designed as an elongated object. Furthermore, the shaft forms the distal section at least partially and preferably at least to a large extent. An “elongated object” is intended to mean, in particular, an object whose main extent is at least a factor of five, preferably at least a factor of ten and particularly preferably at least a factor of twenty larger than a largest extent of the object perpendicular to its main extent, i.e. in particular a diameter of the object. A “main extension” of an object should be understood to mean in particular its longest extension along its main direction of extension. A “main extension direction” of a component is intended to mean, in particular, a direction that runs parallel to a longest edge of a smallest imaginary cuboid, which just completely encloses the component.

An “image capture unit” is to be understood in particular as a unit which is designed to capture images and, for this purpose, includes at least one image capture sensor system. The image capture unit is preferably arranged at least partially and preferably at least to a large extent in the region of the proximal section and/or forms it. Alternatively, it is conceivable that the image capture unit can be arranged at least partially and preferably at least to a large extent in the distal section and/or forms it. Furthermore, the image capture unit could be arranged at least partially distributed over the proximal section and the distal section. The image capture sensor system in particular has at least one image sensor. Furthermore, the image capture sensor system can also have at least two and preferably several image sensors, which can be arranged one behind the other, for example, in the viewing direction of the image capture sensor system. Furthermore, the two and preferably several image capture sensors can have spectral detection sensitivities that are designed differently from one another, so that, for example, a first sensor is particularly sensitive in comparison to a red spectral range, a second sensor is particularly sensitive to comparison in a blue spectral range and a third sensor is particularly sensitive to comparison in a green spectral range. The image sensor can be designed approximately as a CCD sensor. The image sensor is preferably designed as a CMOS sensor. A “viewing direction” of the image capture sensor system is to be understood in particular as a direction which points away from an active side of the image capture sensor system and is preferably at least substantially parallel to the optical axis of the image capture sensor system. “At least essentially parallel” here is intended to mean, in particular, an alignment of a direction relative to a reference direction, in particular in a plane, whereby the direction and the reference direction form an angle of 0°, particularly taking into account a maximum deviation of less than 8°, advantageous of less than 5° and particularly advantageously of less than 2°. Furthermore, the viewing direction could preferably be at least essentially perpendicular to a main extension plane of the image capture sensor system. “At least substantially perpendicular” here is intended to mean, in particular, an alignment of a direction relative to a reference direction, in particular in a plane, where the direction and the reference direction form an angle of 90°, in particular taking into account a maximum deviation of less than 8° , advantageously of less than 5° and particularly advantageously of less than 2°. Under a “main extension plane” of an object is to be understood in particular as a plane which is parallel to a largest side surface of a smallest imaginary cuboid, which just completely encloses the object, and in particular runs through the center of the cuboid. An “optical filter unit” is to be understood in particular as a unit which is intended for filtering optical spectral ranges and which includes at least one spectral filter for this purpose. The spectral filter is designed in particular as a, in particular bandpass filter. Furthermore, the spectral filter could be designed as a polarization filter, preferably as a polarization bandpass filter. A “transmission range of a spectral filter” is intended to mean, in particular, a spectral range of the spectral filter in which it allows at least a large portion of incident light corresponding to the spectrum of the transmission range to pass through. Further spectral ranges of the spectral filter, which are different from the transmission range, should be understood as blocking ranges. An “off-band region of a spectral filter” is intended to mean, in particular, a spectral region of the spectral filter in which it allows at most a fraction of an incident light corresponding to the spectrum of the off-band region to pass. In this context, a “fraction” should be understood to mean in particular less than 10%, preferably less than 5% and particularly preferably less than 1%. The spectral filter is designed in particular as a bandpass filter. The spectral filter preferably has only a single transmission range in an operating state. In particular, the first transmission region and the further first transmission region are never present at the same time in the same operating state of the spectral filter. For example, by transferring the spectral filter from the first operating state to the second operating state, the first transmission range is transferred to the second transmission range and/or vice versa. Furthermore, it is conceivable that the spectral filter can assume further operating states, in particular intermediate states, and light from further transmission ranges can thus be transmitted. For example, operating states of the spectral filter could be continuously changed, whereby continuously different transmission ranges can be achieved. The first transmission region and the second transmission region are in particular spectrally shifted from one another. A degree of shift in the transmission ranges is particularly correlated with the operating state of the spectral filter.

It is further proposed that the first operating state is defined as a first position of the spectral filter relative to the image capture sensor system and the second operating state is defined as a second position of the spectral filter relative to the image capture sensor system. A structure of the spectral filter can advantageously be simplified. Furthermore, a variety of different transmission ranges can be achieved depending on the position of the spectral filter. A “position of the spectral filter relative to the image capture sensor” is intended to mean, in particular, a position and/or orientation in the space of the spectral filter and the image capture sensor relative to one another. In particular, the first position and the second position are different positions of the spectral filter and the image capture sensor relative to one another. The first position and the second position differ approximately by at least one angle between the spectral filter and the image capture sensor system. The angle is spanned in particular by the main extension plane of the spectral filter and a main extension plane of the image capture sensor system. The angle is in particular less than 180°, preferably less than 90° and particularly preferably less than 45°. The angle is more than 0°, preferably more than 5° and particularly preferably more than 10°. In the present case the angle is essentially 30°.

“Substantially” should be understood to mean, in particular, the value taking into account a maximum deviation of at most 10%, preferably at most 5% and particularly preferably at most 2%, or else exactly the value itself. In the first position, the spectral filter is arranged at least substantially perpendicular to the optical axis. Furthermore, particularly in the first position, the image capture sensor is arranged at least substantially perpendicular to the optical axis. It is conceivable that, in particular depending on an overall structure, the spectral filter and the image capture sensor system are arranged at least essentially parallel to one another in the first position. Preferably, in the first position, a main extension plane of the spectral filter is at least essentially parallel to a main extension plane of the image capture sensor system. In the second position, the spectral filter is arranged at an angle to the optical axis. It is conceivable that, in particular depending on an overall structure, the spectral filter and the image capture sensor system are arranged at an angle to one another in the first position. The term angular is intended to mean in particular different from “at least essentially parallel”. In the second position, the angle could preferably be between the main extension plane of the spectral filter and the main extension plane of the image capture sensor system. Furthermore, it is conceivable that the spectral filter and the image capture sensor can be arranged in further positions relative to one another and such light in further transmission areas is transmittable. For example, a position of the spectral filter relative to the image capture sensor could be continuously changed, whereby continuously different transmission ranges can be achieved. The first transmission region and the second transmission region are in particular spectrally shifted from one another. A degree of displacement of the transmission regions is in particular correlated with an angle between the first position and the second position of the spectral filter, the degree of displacement preferably also increasing as the angle increases.

It is further proposed that the first spectral transmission range has a first filter edge and the second spectral transmission range has a second filter edge, which is spectrally shifted relative to the first filter edge. The efficiency of the imaging can advantageously be further improved. In particular, spectral separation of the transmission ranges can be improved. Further advantageously, a sharp separation of the transmission areas can be achieved. A “filter edge” is to be understood in particular as a transition region between an off-band region and a transmission region. In particular, at least the first filter edge and/or the second filter edge is a rising filter edge. A “rising filter edge” is to be understood in particular as a filter edge which describes the transition from an off-band region to a transmission region. In particular, a value of a wavelength of the second filter edge is smaller than a value of a wavelength of the first filter edge. The value of the second filter edge is in particular at least 1%, preferably at least 10% and particularly preferably at least 20% different from the value of the first filter edge and in particular smaller by this factor than the value of the first filter edge.

Furthermore, it is proposed that the first spectral transmission range has a first central wavelength and the second spectral transmission range has a second central wavelength, which is spectrally shifted relative to the first central wavelength. The efficiency of the imaging can advantageously be further improved. In particular, spectral separation of the transmission ranges can be improved. Further advantageously, the transmission ranges can be tuned to intended wavelength ranges. A “central wavelength” is to be understood in particular as the mean value of the spectral transmission range. In particular, a value of a wavelength of the second central wavelength is smaller than a value of a wavelength of the first central wavelength. The value of the second central wavelength is preferably at least 1%, preferably at least 10% and particularly preferably at least 20% different from the value of the first central wavelength and in particular smaller by this factor than the value of the first central wavelength.

It is also proposed that the first spectral transmission range has a first bandwidth and the second spectral transmission range has a second bandwidth, which corresponds at least to a large extent to the first bandwidth. The efficiency of the imaging can advantageously be further improved. In particular, spectral separation of the transmission ranges can be improved. Further advantageously, the transmission ranges can be tuned to intended wavelength ranges. A “bandwidth” is intended to mean, in particular, a width of the spectral transmission range. “To a large extent corresponding” should be understood in particular to mean that an area enclosed by the first transmission region corresponds at least to a large extent to the area enclosed by the second transmission region and preferably overlaps with it at least to a large extent. In particular, a value of a wavelength of the second bandwidth is smaller than a value of a wavelength of the first bandwidth. The value of the second bandwidth is in particular at least 1%, preferably at least 10% and particularly preferably at least 20% different from the value of the first bandwidth and in particular smaller by this factor than the value of the first bandwidth.

It is further proposed that the spectral filter is designed as an interference filter. The efficiency of the imaging can advantageously be further improved. In particular, the wavelength range of transmission spectra can be tailored to an area of application. Furthermore, the spectral filter could be an interference mirror, an interference beam splitter or the like. The interference filter could be designed as a monochromator or a dielectric mirror.

It is further proposed that the image capture unit is set up to transfer the spectral filter from the first operating state to the second operating state and/or vice versa. In order to change the operating state of the spectral filter, in particular relative to the image capture sensor system, the image capture sensor system could be adjustable, for example the image capture unit could have a bearing for this purpose. However, the spectral filter is preferred for changing the operating state of the spectral filter, in particular relative to the image capture sensor system, adjustable. Alternatively, both the spectral filter and the image capture sensors could be adjustable. Particularly preferably, the filter unit has at least one bearing which is designed to support the spectral filter so that it can be transferred from the first operating state to the second operating state and/or vice versa. A part of the installation space or an installation space efficiency can advantageously be improved. The bearing is in particular a pivot and/or tilt bearing. The bearing is in particular intended for pivoting the spectral filter about a pivot axis lying on the main plane of extension of the spectral filter. Furthermore, the bearing could be designed to tilt the spectral filter about a tilt axis lying in the main extension plane.

In one embodiment of the invention, it is proposed that the filter unit comprises at least one actuator, which is designed to transfer the spectral filter from the first operating state to the second operating state and/or vice versa. A component or a space efficiency can advantageously be improved. In particular, complex mechanics for adjusting the spectral filter can be dispensed with. The actuator can in particular be designed as a stepper motor, wherein preferably individual steps of the actuator can correspond to angle segments of the angle between the first operating state and second operating state of the spectral filter, in particular relative to the image capture sensor system. Alternatively or additionally, the image capture unit could have an actuator for adjusting the image capture sensor system.

In a preferred embodiment of the invention, it is proposed that the actuator is designed to transfer the spectral filter from the first operating state to the second operating state of the spectral filter and/or vice versa at least 15 times, preferably at least 30 times and particularly preferably at least 60 times per second . Visualization of image information can advantageously be improved. In particular, moving image information can be recorded, which enables observations in real time. Further advantageously, image information can be provided in real time, which corresponds on the one hand to the first spectral transmission range and on the other hand to the second spectral transmission range. In particular, these can be provided as separate or superimposed image information. Furthermore, the actuator is designed to transfer the spectral filter from the second operating state to the first operating state of the spectral filter at least 15 times, preferably at least 30 times and particularly preferably at least 60 times per second.

In addition, it is proposed that the medical imaging device comprises at least one illumination unit, which is designed to illuminate an object to be captured by the image capture unit. Imaging can advantageously be further improved. In particular, lighting of objects to be examined can be improved. Furthermore, targeted excitation of objects to be examined can be achieved through the lighting provided. The object to be detected can be an object arranged in a cavity, such as tissue, an organ or the like. For lighting purposes, the lighting unit has at least one lighting element. In particular, the lighting unit can have differently designed lighting elements, which can be designed to provide different lighting spectra. For example, a lighting element can be designed as an LED, laser, laser diode, halogen lamp, white light lamp or the like. Alternatively or additionally, the lighting unit can have an illumination filter which is designed to transmit intended illumination spectra, which serve as illumination light of a light source. The object to be illuminated can in particular reflect the illumination spectrum. Furthermore, the object to be illuminated can comprise and/or be provided with spontaneously light-emitting material, which preferably emits light of an emission spectrum based on excitation by the illumination spectrum, which essentially corresponds to an absorption spectrum of the material.

Furthermore, it is proposed that the lighting unit is designed to provide at least a first illumination light according to an illumination spectrum which lies at least to a large extent outside the first spectral transmission range. Imaging can advantageously be further improved. In particular, excitation of spontaneously light-emitting material can be achieved by the illuminating light without the illuminating light significantly superimposing an emission spectrum of the material during imaging. “A large part outside” should be understood here in particular to mean that a large part of an area enclosed by the illumination spectrum lies outside an area enclosed by the transmission range. In particular, the illumination spectrum lies spectrally below the first spectral transmission range.

Furthermore, it is proposed that the illumination spectrum corresponds at least to a large extent to an absorption spectrum of a spontaneously light-emitting material of the material to be illuminated object corresponds. “Corresponding at least to a large extent” should be understood in particular to mean that an area enclosed by the illumination spectrum corresponds at least to a large extent to an area enclosed by the absorption spectrum and preferably overlaps with it at least to a large extent. The spontaneously light-emitting material can in particular be a fluorescent and/or phosphorescent material, in particular a dye. Preferably the spontaneously light-emitting material is part of tissue, such as fluorescent proteins, in particular porphyrins and preferably protoporphyrins. Furthermore, the material can be fluorophores, in particular fluorescein, cyanine or the like, particularly preferably indocyanine green (ICG - Indocyanine green) and/or OTL38.

It is further proposed that an emission spectrum of a spontaneously light-emitting material illuminated by the lighting unit lies at least to a large extent in the first spectral transmission range. Imaging can advantageously be improved. In particular, a large part of the light emitted by the material can be taken into account during imaging. An autofluorescence and/or fluorescence display can thus be achieved, particularly in the first operating state. The emission spectrum is preferably the emission spectrum of the autofluorescent tissue and/or a dye, particularly preferably indocyanine green.

It is further proposed that the lighting unit is designed to provide at least one illumination light with an illumination spectrum, in particular white light, which lies at least to a large extent within the second spectral transmission range. Imaging can advantageously be improved. In particular, a large part of the light reflected by the material can be taken into account during imaging. Thus, particularly in the second operating state, a white light display can be achieved, which is based on the reflection and/or the absorption of spectral components of the illuminating light by the object to be examined. At least “to a large extent within” is intended in particular to mean that at least a large part of an area enclosed by the illumination spectrum lies within an area enclosed by the second transmission region and preferably overlaps with this at least to a large extent.

It is also proposed that a further emission spectrum of a further spontaneously light-emitting material illuminated by the lighting unit lies at least to a large extent outside a first spectral transmission range. Imaging can advantageously be further improved, in which a distinction can be made between the emission spectrum and the further emission spectrum. The term “at least largely outside” is intended to mean, in particular, that at least a large part of an area enclosed by the emission spectrum lies outside an area enclosed by the first transmission region and preferably has no overlap with this area, at least to a large extent.

In addition, it is proposed that a further emission spectrum of a further spontaneously light-emitting material illuminated by the lighting unit lies at least to a large extent within the second spectral transmission range. Imaging can advantageously be further improved, in which a distinction can be made between the emission spectrum and the further emission spectrum. At least “to a large extent within” is intended to mean, in particular, that at least a large part of an area enclosed by the emission spectrum lies within an area enclosed by the second transmission region and preferably overlaps with this at least to a large extent. The further spontaneously light-emitting material is preferably OTL38.

The filter unit can have an imaging lens for imaging transmitted light. It would be conceivable that such an imaging lens could be arranged in front of or behind the spectral filter. However, in order to reduce and/or avoid chromatic imaging errors, it is proposed that the filter unit comprises at least one switchable imaging lens, which is arranged between the spectral filter and the image capture sensor system and which is designed to, depending on an operating state of the spectral filter, a transmission spectrum transmitted by the spectral filter onto the image capture sensor system. A switchable imaging lens is intended to mean, in particular, an imaging lens whose optical properties can be switched, for example by applying a voltage and/or current. The imaging lens could preferably comprise a shape memory material. A focal length of the imaging lens is preferably switchable. The illumination lens in particular had a first switching state in which it comprises a first focal length, which sharply images light onto the image capture sensor system in accordance with the first transmission spectrum. Furthermore, the imaging lens in particular has a second switching state, in which this comprises a second focal length, which is different from the first focal length, and which sharply images light onto the image capture sensor system according to a second transmission spectrum, which is different from the first transmission spectrum.

Furthermore, it is proposed that the filter unit has at least one further spectral filter, which is designed to transmit light in accordance with a further first spectral transmission range in a further first operating state and is designed to transmit light in accordance with a further second spectral transmission range in a further second operating state transmit. Imaging can advantageously be further improved, in which a wide variety of types of spectra can be used for imaging. Except for its optical properties, the further spectral filter is at least essentially identical to the spectral filter. “At least substantially identical” should be understood to mean identical except for manufacturing and/or assembly tolerances. The further first transmission range and the further second transmission range differ from each other in an equivalent manner, as do the first transmission range of the spectral filter and the second transmission range of the spectral filter, in particular with regard to filter edges, bandwidths and/or central wavelength of the respective further transmission range. The optical properties of the spectral filter are selected so that it is designed for autofluorescence imaging in particular in the first operating state and preferably for white light imaging in the second operating state. The optical properties of the further spectral filter are selected so that it is designed in particular in the further first operating state for fluorescence imaging, preferably using indocyanine green, and preferably in the second operating state for further fluorescence imaging, preferably using OTL38. In particular, at least one of the further transmission ranges of the further spectral filter is different from at least one transmission range of the transmission ranges of the further spectral filter. The first transmission range is shifted in the direction of smaller wavelengths, in particular in comparison to the further first transmission range. The first transmission region and the further first transmission region are preferably free of any overlap with one another. The second transmission range is shifted in the direction of smaller wavelengths, in particular in comparison to the further second transmission range. The second transmission region and the further second transmission region are preferably free of any overlap with one another. The transmission areas and the further transmission areas are particularly preferably free of any overlap with one another.

It is further proposed that the image capture unit comprises at least one further image capture sensor system, which is assigned to the further spectral filter and which is arranged in front of the further image capture sensor system when viewed in the viewing direction. Imaging efficiency can advantageously be further improved. In particular, the additional image capture sensor system enables recording with the image capture sensor system, so that various image information can be captured at the same time. The further image capture sensor system is in particular designed to be at least essentially identical to the image capture sensor system. In particular, the image capture unit has a number of image capture sensors which corresponds to the number of spectral filters.

In particular, in order to ensure targeted timing of the image capture unit, it is proposed that the medical imaging device comprises at least one control unit, which is designed to control at least the image capture unit. A “control unit” is to be understood in particular as an electronic unit which comprises at least one processor and preferably a memory. The processor is designed to execute an operating program for operating the image capture device. The operating program is preferably stored in the memory.

It is proposed that the control unit is designed to activate at least one image capture sensor system, in particular the image capture sensor system and/or the further image capture sensor system, of the filter unit depending on at least one operating state of at least one spectral filter, in particular the spectral filter and/or the further spectral filter, or to deactivate. Image capture can advantageously be further improved. In particular, incorrect detection of transmitted light not provided in the transmission region can be avoided by permanently activated image capture sensors. A further advantage is that the flexibility of image capture can be improved. In particular, the control unit controls the respective image capture sensor system in synchronization with a respective operating state of a respective spectral filter. Preferably, the control unit comprises at least one operating mode, to which at least one operating state of at least one spectral filter, in particular relative to the at least one image capture sensor system, is assigned. The number of operating modes corresponds in particular to: which is the number of all possible combinations of the operating states of the spectral filters. The number of operating modes is calculated, for example, from the number of operating states raised to the power of the number of spectral filters. The imaging device preferably has a total of two spectral filters, each with two possible operating states, which in particular results in a number of four different operating modes. In particular, combinations of operating modes result, with simultaneous combinations of operating modes in which the same spectral filter is in different operating states at the same time being excluded. In the preferred case, only operating modes of different spectral filters can be carried out at the same time. An activation or deactivation of the image capture sensor system assigned to the spectral filter is preferably assigned to a respective operating mode. The control unit is designed to operate the operating modes alternately and/or at least partially simultaneously. In the preferred case, in a first operating mode the spectral filter is in the first operating state, in a second operating mode the spectral filter is in the second operating state, in the further first operating mode the further spectral filter is in the further first operating state and in the further second operating mode the further one Spectral filter in the further second operating state. The operating modes are intended in particular to provide various display methods, such as white light display, autofluorescence display and/or fluorescence display. For this purpose, the control unit controls a respective actuator for transferring the positions and/or a respective image capture sensor system in accordance with a clock rate of at least 15 Hz, preferably at least 30 Hz and particularly preferably at least 60 Hz. For example, the control unit could simultaneously alternate between the first operating mode and the second operating mode and / or the further first and further second operating mode. The control unit is designed in particular to provide image information based on the image capture sensed by the image capture sensor system. Preferably, the control unit separates image information recorded from two alternating operating modes into two separate image information items using the same image capture sensor system. For example, the control unit could create image information from different operating modes but the same image capture sensor system for a film with a corresponding frame rate which corresponds to at least 15 Hz, preferably at least 30 Hz and particularly preferably at least 60 Hz. Alternatively or additionally, the control unit could output image information from two or more operating modes together, simultaneously and/or superimposed, in particular as a film with a corresponding frame rate of at least 15 Hz, preferably at least 30 Hz and particularly preferably 60 Hz.

It is also proposed that the control unit is designed to provide at least one illumination light to the filter unit depending on at least one operating state, in particular the operating state and/or the further operating state, of at least one spectral filter, in particular the spectral filter and/or the further spectral filter to activate or deactivate at least one lighting spectrum of the lighting unit. Image capture can advantageously be further improved. In particular, incorrect detection of illumination light that is not intended for a respective transmission range can be avoided by permanently activated lighting. A further advantage is that the flexibility of image capture can be improved. In particular, the control unit controls the respective illumination light or the illumination element of the illumination unit that provides the illumination light in a synchronized manner with a respective operating state of a respective spectral filter, wherein these are preferably additionally synchronized by the control unit with a respective image capture sensor system. The control unit can activate and/or deactivate the lighting light according to a respective operating mode, with activation or deactivation of different lighting spectrums being assigned to different operating modes.

Furthermore, it is proposed that the control unit is designed to activate or deactivate a switching state of the switchable imaging lens depending on at least one operating state of at least one spectral filter. Image capture can advantageously be further improved. In particular, incorrect detection of focal lengths that are not intended for a respective transmission range can be avoided by specifically activating the different switching states of the switchable imaging lens. In particular, the control unit controls a switching state of the imaging lens in synchronization with a respective operating state of a respective spectral filter, which is preferably in turn synchronized by the control unit with a respective image capture sensor system and/or lighting unit. The control unit can assign the imaging lens to different operating modes according to a switching state of the imaging lens.

It is proposed that the medical imaging device at least partially forms a medical imaging device, in particular an endoscopic imaging device. In this way, in particular, a medical imaging device with improved efficiency can be provided.

In a further aspect of the invention, a method for operating a medical imaging device, in particular an endoscopic imaging device, is claimed, in which at least one spectral filter is assigned to an optical filter unit of an image capture sensor system and is arranged in front of the image capture sensor system when viewed in the viewing direction.

It is proposed that in at least one method step the spectral filter transmits light in accordance with a first spectral transmission range to the image capture sensor system in at least a first operating state, in particular relative to the image capture sensor system, and in a further method step the spectral filter transmits light in at least a second operating state, in particular relative to the image capture sensor system transmitted to the image capture sensor system according to a second spectral transmission range, which is at least partially different from the first spectral transmission range.

In this way, in particular, a method for a medical image capture device with improved efficiency can be provided.

The device according to the invention and the method according to the invention should not be limited to the application and embodiment described above. In particular, the device according to the invention and/or the method according to the invention can have a number of individual elements, components and units as well as method steps that deviate from the number of individual elements, components and units as well as method steps mentioned herein in order to fulfill a function of operation described herein. In addition, in the value ranges specified in this disclosure, values lying within the stated limits should also be considered disclosed and can be used in any way.

It is particularly pointed out that all features and properties described in relation to the device, but also procedures, can be transferred to the method according to the invention and can be used in the sense of the invention and are considered to be disclosed. The same applies in the opposite direction. This means that structural features mentioned in relation to the method, i.e. features corresponding to the device, can also be taken into account, claimed and also included in the disclosure within the scope of the device claims.

With regard to optical properties, it should be noted that these can be subject to fluctuations, in particular with regard to fluorescence, which depends on external properties, such as a concentration of a dye, a solvent used for the dye, an intensity of excitation to fluorescence, etc Wavelength for stimulating fluorescence or the like.

If there is more than one example of a particular object, only one of them is provided with a reference number in the figures and in the description. The description of this instance can be transferred to the other instances of the object accordingly. If objects are named in particular using number words, such as first, second, third object, etc., these serve to name and/or assign objects. Accordingly, for example, a first object and a third object, but not a second object, can be included. However, a number and/or a sequence of objects could also be derived from number words.

drawings

Further advantages result from the following drawing description. An exemplary embodiment of the invention is shown in the drawings. The drawings, description and claims contain numerous features in combination. The person skilled in the art will also expediently consider the features individually and combine them into further sensible combinations.

• 1 eine schematische Darstellung einer medizinischen Bildgebungsvorrichtung in einer perspektivischen Ansicht,
• 2 eine schematische Darstellung eines Teils der medizinischen Bildgebungsvorrichtung mit einer Bilderfassungseinheit in einer Draufsicht,
• 3 ein schematisches Diagramm, in welchem optische Eigenschaften der medizinischen Bilderfassungsvorrichtung gemäß eines ersten Betriebszustands eines Spektralfilters relativ zu einer Bilderfassungssensorik der Bilderfassungseinheit dargestellt sind,
• 4 ein schematisches Diagramm, in welchem optische Eigenschaften der medizinischen Bilderfassungsvorrichtung gemäß eines zweiten Betriebszustands eines Spektralfilters relativ zu einer Bilderfassungssensorik der Bilderfassungseinheit dargestellt sind,
• 5 ein schematisches Diagramm, in welchem optische Eigenschaften der medizinischen Bilderfassungsvorrichtung gemäß einsr ersten Betriebszustands eines weiteren Spektralfilters relativ zu einer weiteren Bilderfassungssensorik der Bilderfassungseinheit dargestellt sind,
• 6 ein schematisches Diagramm, in welchem optische Eigenschaften der medizinischen Bilderfassungsvorrichtung gemäß eines zweiten Betriebszustands eines Spektralfilters relativ zu einer Bilderfassungssensorik der Bilderfassungseinheit dargestellt sind,
• 7 einen ersten Betriebsmodus der medizinischen Bildgebungsvorrichtung in einer Draufsicht,
• 8 einen zweiten Betriebsmodus der medizinischen Bildgebungsvorrichtung in einer Draufsicht,
• 9 einen weiteren ersten Betriebsmodus der medizinischen Bildgebungsvorrichtung in einer Draufsicht,
• 10 einen weiteren zweiten Betriebsmodus der medizinischen Bildgebungsvorrichtung in einer Draufsicht,
• 11 einen schematischen Ablaufplan eines beispielhaften Verfahrens zum Betrieb der medizinischen Bildgebungsvorrichtung und
• 12 eine schematische Darstellung einer alternativen medizinischen Bildgebungsvorrichtung in einer perspektivischen Ansicht.

Show it:

• 1 a schematic representation of a medical imaging device in a perspective view,
• 2 a schematic representation of a part of the medical imaging device with an image capture unit in a top view,
• 3 a schematic diagram in which optical properties of the medical image capture device are shown according to a first operating state of a spectral filter relative to an image capture sensor system of the image capture unit,
• 4 a schematic diagram in which optical properties of the medical image capture device are shown according to a second operating state of a spectral filter relative to an image capture sensor system of the image capture unit,
• 5 a schematic diagram in which optical properties of the medical image capture device according to a first operating state of a further spectrum ralfilters are shown relative to a further image capture sensor system of the image capture unit,
• 6 a schematic diagram in which optical properties of the medical image capture device are shown according to a second operating state of a spectral filter relative to an image capture sensor system of the image capture unit,
• 7 a first operating mode of the medical imaging device in a top view,
• 8th a second operating mode of the medical imaging device in a top view,
• 9 a further first operating mode of the medical imaging device in a top view,
• 10 a further second operating mode of the medical imaging device in a top view,
• 11 a schematic flowchart of an exemplary method for operating the medical imaging device and
• 12 a schematic representation of an alternative medical imaging device in a perspective view.

Description of the exemplary embodiments

1 shows a schematic representation of a medical imaging device in a perspective view. In the present case, the medical imaging device is an endoscopic imaging device. Alternatively, the medical imaging device could be an exoscopic, a microscopic or a macroscopic imaging device. The medical imaging device is intended for examining a cavity.

The medical imaging device comprises at least one medical imaging device 70. In the present case, the medical imaging device 70 is an endoscope 72. Alternatively, the medical imaging device 70 could be an exoscope, a microscope and/or a macroscope.

The medical imaging device 70 has a distal section 84. The distal section 84 is designed to be inserted into a cavity in an operating state. The distal section 84 faces a patient in the operating state. The distal section 84 faces away from an operator in the operating state. Furthermore, the medical imaging device 70 has a proximal section 86. The proximal section 86 is arranged outside a cavity in the operating state. The proximal section 86 faces away from a patient in the operating state. The proximal section 86 faces an operator in the operating state.

The medical imaging device 70 has an intermediate section 88. The intermediate section 88 is arranged between the distal section 84 and the proximal section 86.

The medical imaging device has a connection unit 90. The connection unit 90 is part of the medical imaging device 70. The connection unit 90 is arranged in the area of the intermediate section 88. The connection unit 90 is designed to connect the proximal section 86 and the distal section 84 to one another. In the present case, the connection unit 90 is designed to form a positive and/or non-positive connection between the proximal section 86 and the distal section 84, for example by means of a bayonet connection.

The medical imaging device has at least one shaft 92. The shaft 92 is part of the medical imaging device 70. The shaft 92 at least partially forms the distal section 84 of the endoscopic imaging device 70.

Furthermore, the endoscopic imaging device has at least one handle 94. The handle 94 is part of the medical imaging device 70. The handle 94 at least partially forms the proximal section 86 of the medical imaging device 70.

The endoscopic imaging device has at least one image capture unit 10. The image capture unit 10 is part of the medical image capture device 70. The image capture unit 10 is arranged in the area of the proximal section 86. The image capture unit 10 is integrated into the handle 94. Alternatively or additionally, the image capture unit 10 can be arranged at least partially in the area of the distal section 84, in particular in the shaft 92.

2 shows a schematic representation of part of the endoscopic imaging device with the image capture unit 10 in a top view.

To couple in light, the image capture unit 10 includes at least one image frame detection optics unit 96. The image capture optics unit 96 includes at least one optics 102, such as an objective, an eyepiece, a lens, a prism, an optical fiber or the like. The image capture optical unit 96 defines an input beam path 100.

The image capture optical unit 96 has at least one beam splitter 98. In the present case, the beam splitter 98 is designed as an interference beam splitter. Viewed in the direction of incidence of the input beam path 100, the beam splitter 98 is arranged in front of the optics 102. The beam splitter 98 divides the input beam path 100 into at least two beam paths 104, 106, namely one beam path 104 and another beam path 106. The beam splitter 98 divides the input beam path 100 essentially equally into the two beam paths 104, 106. Alternatively, the beam splitter 98 could also divide the input beam path 100 into different parts.

The image capture unit 10 has at least one image capture sensor system 12. The image capture sensor system 12 is designed to record image information at a frame rate of at least 15 images per second. In the present case, the image capture sensor system 12 is even designed to record at least 30 images per second. The image capture sensor system 12 includes at least one image sensor 14. In the present case, the image sensor is designed as a CMOS sensor. The image capture sensor system can have multiple image capture sensors. Alternatively or additionally, at least one image sensor 14 of the image capture sensor system 12 can be designed as a CCD sensor.

The endoscopic imaging device comprises at least one optical filter unit 16. The optical filter unit 16 is at least partially arranged between the image capture optical unit 98 and the image capture sensor system 12. The optical filter unit 16 comprises at least one spectral filter 18. The spectral filter 18 is arranged between the optics 102 and the image capture sensor system 12. The spectral filter 18 is arranged between the beam splitter 98 and the image capture sensor system 12. The spectral filter 18 is assigned to the image capture sensor system 12. The spectral filter 18 is arranged in front of the image capture sensor system 12 when viewed in a viewing direction 20 of the image capture sensor system 12. The spectral filter 18 is designed as an interference filter 38. Furthermore, the spectral filter 18 is a band filter. In the present case, the spectral filter 18 is designed separately from the beam splitter 98. However, it would be conceivable that the beam splitter 98 could form the spectral filter 18, whereby components and/or installation space can advantageously be reduced, since in particular a further spectral filter could also be dispensed with.

The spectral filter 18 has at least two operating states. In the present case, the operating states are positions of the spectral filter 18 relative to the image capture sensor system 12. The spectral filter 18 has a first operating state. The first operating state is defined as a first position of the spectral filter 18 relative to the image capture sensor system 12. Furthermore, the spectral filter 18 has a second operating state. The second operating state of the spectral filter 18 is defined as a second position of the spectral filter 18 relative to the image capture sensor system 12. The spectral filter 18 can be transferred from the first operating state to the second operating state. The spectral filter 18 can be transferred from the second operating state to the first operating state. Further operating states, in particular positions of the spectral filter 18 relative to the image capture sensor system 12, are also conceivable, which could each have different transmission ranges. For example, the spectral filter 18 could also be continuously adjustable relative to the image capture sensor system 12. Alternatively, it would also be conceivable that in order to vary a position of the spectral filter 18 relative to the image capture sensor system 12, the image capture sensor system 12 can be moved from a first position to a second position and vice versa instead of the spectral filter 18.

In the present case, the spectral filter 18 can be tilted to transfer from the first operating state to the second operating state. Furthermore, the spectral filter 18 can be tilted back from the second operating state to the first operating state. The spectral filter 18 has a main extension plane 108. In the present case, the spectral filter 18 can be pivoted about a pivot axis 110, which is at least substantially parallel to the main extension plane 108. In the present case, the pivot axis 110 is defined by a side edge of the spectral filter 18. Alternatively, it is conceivable that the spectral filter 18 can be rotatable/tiltable, in particular about a yaw, elevation and/or vertical axis of the spectral filter 18.

The first operating state and the second operating state are defined by mutually different positions of the spectral filter 18 relative to the image capture sensor system 12. The first operating state and the second operating state differ by a respective orientation of a position of the spectral filter 18 relative to the image capture sensor system 12. The image capture sensor system 12 has a main extension plane 112 on. In the first operating state of the spectral filter 18, the main extension plane 108 of the spectral filter 18 is at least substantially perpendicular to the optical axis. In the present case, in the first Operating state of the spectral filter, the main extension plane 108 of the spectral filter 18 is at least substantially perpendicular to a main extension plane 112 of the image capture sensor system 12. In the second operating state of the spectral filter 18, the main extension plane 108 of the spectral filter 18 is angular to the optical axis. Furthermore, in the second operating state of the spectral filter 18, the main extension plane 108 of the spectral filter 18 is angular to the main extension plane of the image capture sensor system 12. In the second operating state, an angle between the main extension plane 108 of the spectral filter 18 and the optical axis of the image capture sensor system 12 is at least 92 °. The angle is also a maximum of 135°. In the present case the angle is essentially 115°. Furthermore, in the second operating state, an angle between the main extension plane 108 of the spectral filter 18 and the main extension plane 112 of the image capture sensor system 12 is at least 2°. The angle is also a maximum of 45°. In the present case the angle is essentially 25°.

The spectral filter can be transferred from the first operating state to the second operating state. For this purpose, the filter unit 16 has at least one bearing 40. The bearing 40 is designed to store the spectral filter 18 so that it can be transferred from the first operating state to the second operating state and/or vice versa. In the present case, the bearing 40 is designed as a pivot bearing. Furthermore, the bearing 40 could also be designed as a tilt and/or pivot bearing. Alternatively or additionally, the bearing 40 could serve to provide an adjustable mounting of the image capture sensor system 12.

The filter unit 16 has at least one actuator 42. The actuator 42 is designed to transfer the spectral filter 18 from the first operating state to the second operating state and/or vice versa. The actuator 42 is designed to transfer the spectral filter 18 from the first operating state to the second operating state of the spectral filter 18 at least 15 times per second. The actuator 42 is further designed to transfer the spectral filter 18 from the second operating state to the first operating state of the spectral filter 18 at least 15 times per second. Accordingly, the operating states of the spectral filter 18 change at least 30 times per second. The actuator 42 is designed, for example, as a stepper motor. Steps of the actuator 42 correspond to angle segments of the angle between the first operating state and the second operating state of the spectral filter 18 relative to the image capture sensor system 12.

3 shows a schematic diagram 116, in which optical properties of the medical image capture device according to the first operating state of the spectral filter 18, in particular relative to the image capture sensor system 12, are shown. The diagram 116 has an abscissa axis 118. A wavelength is plotted on the abscissa axis 118. The wavelength is plotted linearly on the abscissa axis 118. The wavelength is plotted on the abscissa axis 118 in the unit nm. A shown range of the abscissa axis 118 extends from a minimum value 120 to a maximum value 122. The minimum value 120 is 350 nm. The maximum value 122 is 1050 nm. The diagram 116 has an ordinate axis 124. An intensity is plotted on the ordinate axis 124. The intensity is plotted linearly on the ordinate axis. The intensity is plotted standardized on the ordinate axis 124. For this purpose, the intensity curves shown in diagram 116 are normalized to their corresponding intensity maximum. The intensity is indicated on the ordinate axis 124 in arbitrary units au (arbitrary units). A shown range of the ordinate axis 124 extends from a minimum value 126 to a maximum value 128. The minimum value 126 is 0. The maximum value 128 is 1.

In the first operating state, the spectral filter 18 has a first transmission region 22. The transmission range is according to an intensity curve in diagram 126 3 shown. In the first operating state, the spectral filter 18 is designed to transmit light to the image capture sensor system 12 in accordance with the first spectral transmission range 22. The first spectral transmission range 22 has a first filter edge 26. The first filter edge 26 is essentially at 430 nm. The first filter edge 26 is a rising filter edge. The first spectral transmission range 22 has a first central wavelength 30. The central wavelength 30 is essentially 575 nm. Furthermore, the first transmission region 22 has a further first filter edge 27. The further first filter edge 27 is essentially at 725 nm. The further first filter edge 27 is a falling filter edge. The first spectral transmission range 22 has a first bandwidth 34. The first bandwidth 34 is essentially 295 nm.

4 shows a schematic diagram 130, in which optical properties of the medical image capture device according to the second operating state of the spectral filter 18, in particular relative to the image capture sensor system 12, are shown. The diagram 130 has an abscissa axis 132. A wavelength is plotted on the abscissa axis 132. The wavelength is plotted linearly on the abscissa axis 132. The wavelength is on the abscissa axis 132 in the Unit nm plotted. A shown range of the abscissa axis 132 extends from a minimum value 134 to a maximum value 136. The minimum value 134 is 350 nm. The maximum value 136 is 1050 nm. The diagram 116 has an ordinate axis 138. An intensity is plotted on the ordinate axis 138. The intensity is plotted linearly on the ordinate axis 138. The intensity is plotted standardized on the ordinate axis 138. For this purpose, the intensity curves shown in the diagram are normalized to their corresponding intensity maximum. The intensity is indicated on the ordinate axis 138 in arbitrary units au (arbitrary units). A shown range of the ordinate axis 138 extends from a minimum value 140 to a maximum value 142. The minimum value 140 is 0. The maximum value 142 is 1.

In the second operating state, the spectral filter 18 is designed to transmit light to the image capture sensor system 12 in accordance with a second spectral transmission range 24. The transmission range is according to an intensity curve in diagram 130 4 shown. The second spectral transmission range 24 has a second filter edge 28. The second filter edge 28 is a rising filter edge. The second filter edge 28 is essentially at 400 nm. The second spectral transmission range 24 has a second central wavelength 32. The second central wavelength 32 is essentially at 542 nm. The further second filter edge 29 is essentially at 670 nm. The second spectral transmission range 24 has a further second filter edge 29. The further second filter edge 29 is a falling filter edge. The second spectral transmission range 24 has a second bandwidth 36. The second bandwidth is essentially 283 nm.

The second spectral transmission range 24 is at least partially different from the first spectral transmission range 22. The second filter edge 28 is spectrally shifted relative to the first filter edge 26. The second filter edge 28 is shifted by essentially 30 nm to the first filter edge 26. The second central wavelength 32 is spectrally shifted relative to the first central wavelength 30. The second central wavelength 32 is shifted from the first central wavelength 30 by essentially 33 nm. The second bandwidth 36 is at least partially different from the first bandwidth 34. The second bandwidth 36 is smaller than the first bandwidth 34. The second bandwidth 36 is essentially 5% smaller than the first bandwidth 34. The second bandwidth 36 is essentially 12 nm smaller than the first bandwidth 34. The second bandwidth 36 corresponds at least to a large extent to the first bandwidth 34. The second bandwidth 36 overlaps at least 90% with the first bandwidth 34.

The lighting unit 44 is designed to provide at least a first illumination light according to a first illumination spectrum 46. The first illumination spectrum 46 is according to an intensity curve in diagram 116 3 shown. For this purpose, the lighting unit 44 has at least one first lighting element, such as an LED, a laser diode, a laser or the like, which emits light according to the lighting spectrum 46. The first illumination spectrum 46 has a Gaussian intensity curve. The first illumination spectrum 46 has a peak 148. In the present case, the peak 148 is essentially at 410 nm. The first illumination spectrum 46 lies at least to a large extent outside the first spectral transmission range 22 in the first operating state of the spectral filter 18 relative to the image capture sensor system 12. Accordingly, in the first operating state of the spectral filter 18, In particular, relative to the image capture sensor system 12, light is filtered out at least to a large extent according to the first illumination spectrum. In contrast, the illumination spectrum 46 lies at least to a large extent within the second spectral transmission range 24 in the second operating state of the spectral filter 18, in particular relative to the image capture sensor system 12 (cf. 4 ).

A first absorption spectrum 48 of a spontaneously light-emitting material of an object to be detected is according to an intensity curve in diagram 116 3 shown. The first illumination spectrum 46 corresponds at least to a large extent to the first absorption spectrum 48 of the spontaneously light-emitting material of the object to be detected. In the present case, the spontaneously light-emitting material of the sensing object is tissue that exhibits autofluorescence. The tissue includes porphyrin, in particular protoporphyrin. The first absorption spectrum 48 lies at least to a large extent outside the first spectral transmission range 22 in the first operating state of the spectral filter 18, in particular relative to the image capture sensor system 12. In particular, in contrast, the first absorption spectrum 48 lies at least to a large extent within the second spectral transmission range 24 in the second operating state of the spectral filter 18, in particular relative to the image capture sensor system 12 (cf. 4 ).

An emission spectrum 52 of the spontaneous light-emitting material illuminated by the lighting unit 44 is according to an intensity course in diagram 116 in a range from essentially 620 nm to essentially 750 nm in the 3 shown. The emission spectrum 52 of the spontaneously light-emitting material illuminated by the lighting unit 44 lies at least to a large extent in the first spectral transmission range 22. Accordingly, light of the emission spectrum 52 emitted by the spontaneously light-emitting material of the detecting object can at least largely cover the first transmission range 22 of the spectral filter 18 happen. In particular, in contrast to this, the emission spectrum 52 lies at least to a large extent outside the second spectral transmission range 24 in the second operating state of the spectral filter 18, in particular relative to the image capture sensor system 12 (cf. 4 ).

The lighting unit 44 is designed to provide at least a second illumination light of a second illumination spectrum 47. The second illumination spectrum 47 is according to an intensity curve in diagram 130 4 shown. For this purpose, the lighting unit 44 has at least one second lighting element. The second lighting element is a white light source, such as an LED tube lamp, a fluorescent lamp or the like. The second illumination spectrum 47 lies at least to a large extent within the second spectral transmission range 24. The second illumination spectrum 47 is a white light spectrum. Accordingly, the second spectral transmission range 24 allows light to pass at least to a large extent according to the second illumination spectrum 47. In particular, in contrast, the second illumination spectrum 47 lies at least partially outside the first transmission range 22.

As in 2 shown, the image capture unit 10 has at least one further image capture sensor system 62. The further image capture sensor system 62 is at least essentially identical to the image capture sensor system 12. The further image capture sensor system 62 has at least one further image sensor 15. The further image capture sensor system 62 is arranged in the further beam path 106. The further image capture sensor system 62 is arranged offset from the image capture sensor system 12. The further image capture sensor system 62 has a main extension plane 144. In the present case, the main extension plane 144 of the further image capture sensor system 62 is at least essentially perpendicular to the main extension plane 112 of the image capture sensor system 12.

The filter unit 16 has at least one further spectral filter 64. In the present case, the further spectral filter 64 is designed differently from the spectral filter 18. The further spectral filter 64 differs from the spectral filter 18 in its optical properties. In the event that the beam splitter 98 forms the spectral filter 18, this would also form the further spectral filter 64.

The further spectral filter 64 is arranged in the further beam path 106. The further image capture sensor system 62 is assigned to the further spectral filter 64. The further spectral filter 64 is arranged in front of it when viewed in a viewing direction 66 of the further image capture sensor system 62. A main extension plane 146 of the further spectral filter 64 is at least essentially parallel to the main extension 108 of the further spectral filter 64 in at least one operating state of the spectral filter 12.

The further spectral filter 64 has at least two operating states, in particular relative to the further image capture sensor system 62, namely a further first operating state and a further second operating state. The further first operating state and the further second operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62, are equivalent to the first operating state and the second operating state of the spectral filter 18 to the image capture sensor system 12.

To store the further spectral filter 64, the filter unit 16 has at least one further bearing 41. The further bearing 41 is at least essentially identical to the bearing 40. To transfer the further spectral filter 64 from the further first operating state to the further second operating state and vice versa, the filter unit 16 has at least one further actuator 43. The further actuator 43 is at least essentially identical to the actuator 42.

5 shows a schematic diagram 160, in which optical properties of the medical image capture device according to the first operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62, are shown. The diagram 160 has an abscissa axis 162. A wavelength is plotted on the abscissa axis 162. The wavelength is plotted linearly on the abscissa axis 162. The wavelength is plotted on the abscissa axis 162 in the unit nm. A shown range of the abscissa axis 162 extends from a minimum value 164 to a maximum value 166. The minimum value 164 is 350 nm. The maximum value 166 is 1250 nm. The diagram 160 has an ordinate axis 168. An intensity is plotted on the ordinate axis 168 gen. The intensity is plotted linearly on the ordinate axis 168. The intensity is plotted standardized on the ordinate axis 168. For this purpose, intensity curves shown in diagram 160 are normalized to their corresponding intensity maximum. The intensity is indicated on the ordinate axis 168 in arbitrary units au (arbitrary units). A shown range of the ordinate axis 168 extends from a minimum value 170 to a maximum value 172. The minimum value 170 is 0. The maximum value 172 is 1.

In the first operating state, the further spectral filter 64 has a further first spectral transmission range 56. The further first spectral transmission range 56 is according to an intensity curve in diagram 160 5 shown. In the further first operating state, the further spectral filter 64 is designed to transmit light in accordance with the further first spectral transmission range 56 to the further image capture sensor system 62. The further first spectral transmission range 56 has a further first filter edge 174. The further first filter edge 174 is essentially at 800 nm. The further first filter edge 174 is a rising filter edge. The further first spectral transmission range 56 has a further first central wavelength 176. The further first central wavelength 176 is essentially at 950 nm. Furthermore, the further first transmission region 56 has a further further first filter edge 178. The further further first filter edge 178 is essentially at 1100 nm. The further further first filter edge 178 is a falling filter edge. The further first spectral transmission range 56 has a further first bandwidth 180. The further first bandwidth 180 is essentially 300 nm.

6 shows a schematic diagram 182, in which optical properties of the medical image capture device according to the further second operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62, are shown. The diagram 182 has an abscissa axis 184. A wavelength is plotted on the abscissa axis 184. The wavelength is plotted linearly on the abscissa axis 184. The wavelength is plotted on the abscissa axis 184 in the unit nm. A shown range of the abscissa axis 184 extends from a minimum value 186 to a maximum value 188. The minimum value 186 is 350 nm. The maximum value 188 is 1250 nm. The diagram 182 has an ordinate axis 190. An intensity is plotted on the ordinate axis 190. The intensity is plotted linearly on the ordinate axis 190. The intensity is plotted standardized on the ordinate axis 190. For this purpose, intensity curves shown in diagram 182 are normalized to their corresponding intensity maximum. The intensity is indicated on the ordinate axis 190 in arbitrary units au (arbitrary units). A shown range of the ordinate axis 190 extends from a minimum value 192 to a maximum value 194. The minimum value 192 is 0. The maximum value 194 is 1.

In the further second operating state, the further spectral filter 64 is designed to transmit light to the further image capture sensor system 62 in accordance with a further second spectral transmission range 60. The further second spectral transmission range 60 is according to an intensity curve in diagram 182 6 shown. The further second spectral transmission range 60 has a further second filter edge 196. The further second filter edge 196 is a rising filter edge. The further second filter edge 196 is essentially at 770 nm. The further second spectral transmission range 60 has a further second central wavelength 198. The further second central wavelength 198 is essentially at 900 nm. The further second spectral transmission range 60 has a further second filter edge 200. The further second filter edge 200 is a falling filter edge. The further second filter edge 200 is essentially at 1030 nm. The further second spectral transmission range 60 has a further second bandwidth 202. The further second bandwidth 202 is essentially 283 nm.

The further second spectral transmission range 60 is at least partially different from the further first spectral transmission range 56. The further second filter edge 200 is spectrally shifted relative to the further first filter edge 174. The further second filter edge 200 is shifted by essentially 30 nm to the further first filter edge 174. The further second central wavelength 198 is spectrally shifted relative to the further first central wavelength 176. The further second central wavelength 198 is shifted from the further first central wavelength 176 by essentially 30 nm. The further second bandwidth 202 is at least partially different from the further first bandwidth 180. The further second bandwidth 202 is smaller than the further first bandwidth 180. The further second bandwidth 202 is essentially 5% smaller than the further first bandwidth 180. The further second bandwidth 202 is essentially 30 nm smaller than the further first bandwidth 180. The further second bandwidth 202 corresponds at least to a large extent to the further first bandwidth 180. The further second band Width 202 overlaps at least 90% with the further first bandwidth 180.

The lighting unit 44 is designed to provide at least one further first illumination light according to a further first illumination spectrum 204. The further first illumination spectrum 204 is according to an intensity curve in diagram 160 5 shown. For this purpose, the lighting unit 44 has at least one further first lighting element, such as an LED, a laser diode, a laser or the like, which emits light according to the further first lighting spectrum 204. The further first illumination spectrum 204 has a Gaussian intensity curve. The further first illumination spectrum 204 has a peak 206. In the present case, the peak 206 is essentially at 770 nm. The further first illumination spectrum 204 lies at least partially and preferably at least to a large extent outside the first spectral transmission range 56 in the further first operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62. Accordingly, in the further first operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62, light according to the further first illumination spectrum 204 is at least largely filtered out. In particular, in contrast to this, the further first illumination spectrum 204 lies at least to a large extent within the further second spectral transmission range 60 in the second operating state of the further spectral filter 18, in particular relative to the further image capture sensor system 62 (cf. 6 ).

A further first absorption spectrum 208 of a further first spontaneously light-emitting material of an object to be detected is according to an intensity profile in diagram 160 5 shown. The further first illumination spectrum 204 corresponds at least to a large extent to the further first absorption spectrum 208 of the further first spontaneously light-emitting material of the object to be detected. In the present case, the further first spontaneously light-emitting material is a fluorescent dye. The fluorescent dye is indocyanine green. The further first absorption spectrum 208 lies at least to a large extent outside the further first spectral transmission range 56 in the further first operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 13. In particular, in contrast to this, the further first absorption spectrum 208 lies at least to a large extent within the further second spectral transmission range 60 in the further second operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62 (cf. 5 ).

A further first emission spectrum 54 of the further first spontaneously light-emitting material illuminated by means of the lighting unit 44 is in a range from 750 nm to 900 nm according to an intensity profile in diagram 130 4 shown. The further first emission spectrum 54 of the further first spontaneous light-emitting material illuminated by means of the lighting unit 44 lies at least to a large extent in the further first spectral transmission range 56. Accordingly, light of the further first emission spectrum 54 emitted by the further first spontaneous light-emitting material can be at least to a large extent pass through the further first transmission region 56 of the further spectral filter 64.

The lighting unit 44 is designed to provide at least one further second illumination light according to a further second illumination spectrum 210. The further second illumination spectrum 210 is according to an intensity curve in diagram 182 6 shown. For this purpose, the lighting unit 44 has at least one further second lighting element, such as an LED, a laser diode, a laser or the like, which emits light according to the further second lighting spectrum 210. The further second illumination spectrum 210 has a Gaussian intensity curve. The further second illumination spectrum 201 has a peak 212. In the present case, the peak 212 is essentially at 745 nm. The further second illumination spectrum 210 lies at least to a large extent outside the further second spectral transmission range 60 in the further second operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62. Accordingly, in In the further second operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62, light is filtered out at least to a large extent according to the further first illumination spectrum 204.

A further second absorption spectrum 214 of a further second spontaneously light-emitting material of an object to be detected is according to an intensity profile in diagram 160 5 shown. The further second illumination spectrum 210 corresponds at least to a large extent to the further second absorption spectrum 214 of the further second spontaneously light-emitting material. In the present case, the further second spontaneously light-emitting material is a fluorescent dye. The fluorescent dye is OTL38. The further second absorption spectrum 214 is at least one Large part outside the further second spectral transmission range 60 in the second operating state of the further spectral filter 64, in particular relative to the further image capture sensor system 62.

A further second emission spectrum 55 of the further second spontaneously light-emitting material illuminated by means of the lighting unit 44 is in a range from 800 nm to 900 nm according to an intensity curve in diagram 182 6 shown. The further second emission spectrum 55 of the further second spontaneous light-emitting material illuminated by means of the lighting unit 44 lies at least to a large extent in the further second spectral transmission range 60. Accordingly, light of the further second emission spectrum 55 emitted by the further second spontaneous light-emitting material of the detecting object can at least to a large extent pass through the further second transmission region 60 of the further spectral filter 64.

1 further shows a control unit 68 of the medical imaging device. The control unit 68 is designed to control further components of the medical imaging device. In the present case, the control unit 68 forms a separate control device 82. Alternatively, the control unit 68 could be part of the medical imaging device 70 and/or be arranged in a common housing with the lighting unit 44. The control unit 68 includes at least one control electronics (not shown). The control electronics includes at least one processor. Furthermore, the control unit 68 includes at least one memory. An operating program is stored in the memory. The processor is designed to execute the operating program.

The control unit 68 is designed to control the lighting unit 44. For this purpose, the control unit 68 is electrically and/or electronically connected to the lighting unit 44. The control unit 68 is designed to activate and/or deactivate the first lighting element, the second lighting element, the further first and/or further second lighting element depending on an operating mode in order to provide lighting light of a respective lighting spectrum.

The control unit 68 is designed to control the image capture unit 10. The control unit 68 is electrically and/or electronically connected to the image capture unit 10. The control unit 68 controls the actuators in order to transfer the spectral filters to the respective first and/or second operating state, in particular relative to the respective image capture sensors. The control unit 68 controls the image capture sensor system 12 and/or the further image capture sensor system 62.

In particular, the control unit 68 activates and/or deactivates the image capture sensor system 12 and/or the further image capture sensor system 62.

7 until 10 show various possible combinations of the operating states of the spectral filters 18, 64 relative to one another, as well as in different operating modes. In 7 the spectral filter 18 is in the first operating state. This corresponds to a first operating mode. The further spectral filter 64 is in the further first operating state. This corresponds to another first operating mode.

In 8th the spectral filter 18 is in the second operating state. This corresponds to a second operating mode. The further spectral filter 64 is in the first operating state. This corresponds to another first operating mode.

In 9 the spectral filter 18 is in the first operating state. This corresponds to the first operating mode. The further spectral filter 64 is in the further second operating state. This corresponds to a further second operating mode.

In 10 the spectral filter 18 is in the second position. This corresponds to the first operating state. The further spectral filter 64 is in the further second operating state.

The control unit 68 is designed to activate or deactivate at least one image capture sensor system 12 at least one of the spectral filters 18, 64 of the filter unit 16 depending on at least one operating state. For this purpose, the control unit 68 controls the spectral filters 18, 64 and the image capture sensor system 12 in a synchronized manner. Furthermore, the control unit 68 is designed to activate or deactivate at least one illumination light according to at least one illumination spectrum of the illumination unit 44 depending on an operating state of the spectral filters 18, 64. For this purpose, the control unit 68 controls the spectral filters 18, 64 and the lighting unit in a synchronized manner.

The medical imaging device further has at least one display unit 74. The display unit 74 is designed to display image information captured with the medical imaging device 70. In the present case, the display unit 74 forms a separate display device 76. Alternatively, the display unit 74 could be part of the medical imaging device 70. The control unit 68 is designed to control the display unit 74. For this purpose, the control unit 68 is electrically and/or electronically connected to the display unit 74. The control unit 68 is designed to provide the display unit 74 with image information captured by the image capture unit depending on an operating mode.

11 shows a schematic flowchart of an exemplary method for operating the medical imaging device. The method is part of an operating program which is stored and executable in the control unit 68.

The method has a first method step 218. In method step 218, an imaging function 228 is started.

The imaging function 228 includes at least one further method sub-step. In the further method sub-step 220, a first operating mode is used. In the first operating mode, the control unit 68 controls the first lighting element. Furthermore, the control unit 68 controls the actuator 42 so that the spectral filter is transferred to or is in the first operating state. Furthermore, the control unit 68 controls the image capture sensor system 12. The control unit 68 activates the first lighting element so that this lighting light is provided in accordance with its first lighting spectrum 46. The illuminating light hits an object to be examined. The first illumination spectrum 46 is at least partially absorbed by the object to be examined. The first illumination spectrum 46 stimulates the object to be examined to autofluoresce. In the first operating state, the first spectral transmission range 22 essentially corresponds to the first emission spectrum 52 of the autofluorescence. Furthermore, the control unit 68 activates the image capture sensor system 12. The image capture sensor system 12 senses light from image information corresponding to the first spectral transmission range 22.

The imaging function 228 includes at least one further method sub-step 222. In the further method sub-step 222, a second operating mode is used. The control unit 68 controls the actuator 42 in such a way that it transfers the spectral filter 18 to the second operating state or is in this. Furthermore, the control unit 68 controls the image capture sensor system 12. The control unit 68 activates the second lighting element so that it provides second lighting light corresponding to its second lighting spectrum 47. The second illumination light hits an object to be examined. The second illumination spectrum 47 is at least partially reflected by the object to be examined. In the second operating state of the spectral filter 18, the second spectral transmission range 24 essentially corresponds to the reflection spectrum of the illumination light reflected by the object to be examined. Furthermore, the control unit 68 activates the image capture sensor system 12. The image capture sensor system 12 senses light from image information corresponding to the second spectral transmission range 24.

The method has a further step 224. In the further process step 224, a further first operating mode is used. The control unit 68 controls the further actuator 43 in such a way that it transfers the further spectral filter 64 into the further first operating state or that it is in this. Furthermore, the control unit 68 controls the further image capture sensor system 13. The control unit 68 activates the further first lighting element so that it provides further first lighting light in accordance with its further first lighting spectrum. The further first illumination light hits the object to be examined. The object to be examined includes a further first spontaneously light-emitting material. In the present case, the further first spontaneously light-emitting material is indocyanine green. The further first illumination spectrum 204 is at least partially absorbed by the object to be examined. The further first illumination spectrum 204 corresponds at least to a large extent to a further first absorption spectrum 208 of the further first spontaneously light-emitting material. In the further first operating state, the further first spectral transmission range 56 essentially corresponds to a further first emission spectrum 54 of the further first spontaneously light-emitting material. Furthermore, the control unit activates the additional image capture sensors. The further image capture sensor system 13 senses light from image information corresponding to the further first spectral transmission range 56.

The method has a further partial method step 226. In the further method sub-step 226, a further second operating mode is used. The control unit 68 controls the further actuator 43 in such a way that the further spectral filter 64 is transferred to the further second operating state or is in this. Furthermore, the control unit 68 controls the further image capture sensors 13. The control unit 68 activates the further second lighting element, so that this further second illumination light is provided in accordance with its further second illumination spectrum 210. The additional second illumination light hits the object to be examined. The object to be examined includes another second spontaneous light emitting material. In the present case, the further second spontaneously light-emitting material is OTL38. The further second illumination spectrum 210 is at least partially absorbed by the further second spontaneous light-emitting material. The further second illumination spectrum 210 corresponds at least to a large extent to a further second absorption spectrum 210 of the further second spontaneously light-emitting material. In the further second operating state, the further second spectral transmission range 60 essentially corresponds to a further second emission spectrum 55 of the further second spontaneously light-emitting material. Furthermore, the control unit 68 activates the further image capture sensor system 13. The further image capture sensor system 13 senses light from image information corresponding to the further second spectral transmission range 60.

To carry out the imaging function, the control unit 68 carries out the aforementioned method sub-steps alternately or simultaneously as required, so that corresponding simultaneous provision of different image information from different operating modes and thus different spectral transmission ranges and illumination spectra is achieved. The image information is made available to the display unit. The image information provided is displayed on the display unit. The control unit 68 provides the display unit with image information as a film with at least a frame rate of 15 frames per second for each operating mode. Furthermore, the control unit 68 can combine the image information of at least two different operating modes and make it available as a combined film with at least a frame rate of 30 frames per second.

The method includes a further method step 230. In the further method step 230, the imaging function 228 is ended.

In 12 Another embodiment of the invention is shown. The following descriptions and the drawings are essentially limited to the differences between the exemplary embodiments, with regard to components with the same designation, in particular with regard to components with the same reference numerals, in principle also to the drawings and / or the description of the other exemplary embodiments, in particular the 1 until 11 is referred. To distinguish between the exemplary embodiments, see: 12 which follows the reference number of the letter a.

12 shows another embodiment of the invention. The present exemplary embodiment differs from the previous one essentially in a design of the image capture unit 10a. In the present case, the filter unit 16a has a switchable imaging lens 58a. The switchable imaging lens 58a is arranged between the spectral filter 18a and the image sensor 14a. The switchable imaging lens 58a is intended to reduce or avoid chromatic imaging errors when using different transmission spectra. The switchable imaging lens 58a is designed to image a transmission spectrum transmitted by the spectral filter 18a onto the image capture sensor system 12a, depending on an operating state of the spectral filter 18a. The switchable imaging lens 58a can be switched in terms of its optical properties, for example by applying a voltage and/or a current. For example, the switchable imaging lens 58a may include a shape memory material. In the present case, a focal length of the switchable imaging lens 58a can be switched. The switchable imaging lens 58a in particular has a first switching state in which it includes a first calorific value, which sharply images light onto the image capture sensor system 12a in accordance with the first transmission spectrum. Furthermore, the switchable imaging lens 58a has a second switching state in which it comprises a second focal length, which is different from the first focal length, and which sharply images light onto the image capture sensor 12a according to a second transmission spectrum, which is different from the first transmission spectrum. The switchable imaging lens 58a is electrically and/or electronically connected to the control unit. The switchable imaging lens 58a can be controlled or switched using the control unit.

Furthermore, the filter unit 16a has at least one further switchable imaging lens 59a. The further switchable imaging lens 59a is arranged between the further spectral filter 18a and the further image capture sensor system 62a. The further switchable imaging lens 59a in particular has a further first switching state in which it comprises a further first calorific value, which sharply images light onto the further image capture sensor system 62a in accordance with the further first transmission spectrum. Furthermore, the further switchable imaging lens 59a has a further second switching state, in which it comprises a second focal length, which is different from the further first focal length, and which sharply focuses light according to a further second transmission spectrum, which is different from the further first transmission spectrum which depicts further image capture sensors 62a. The switchable imaging lens 58a is electrically and/or electronically connected to the control unit. The Switchable imaging lens 58a can be controlled or switched by means of the control unit.

10

Bilderfassungseinheit

12

Bilderfassungssensorik

13

Weitere Bilderfassungssensorik

15

Weiterer Bildsensor

14

Bildsensor

16

Filtereinheit

18

Spektralfilter

20

Blickrichtung

22

Erster spektraler Transmissionsbereich

24

Zweiter spektraler Transmissionsbereich

26

Erste Filterkante

27

Weitere erste Filterkante

28

Zweite Filterkante

29

Weitere zweite Filterkante

30

Erste Zentralwellenlänge

32

Zweite Zentralwellenlänge

34

Erste Bandbreite

36

Zweite Bandbreite

38

Interferenzfilter

40

Lager

41

Lager

42

Aktor

43

Weiterer Aktor

44

Beleuchtungseinheit

46

Erstes Beleuchtungsspektrum

47

Zweites Beleuchtungsspektrum

48

Absorptionsspektrum

52

Emissionsspektrum

54

Weiteres erstes Emissionsspektrum

55

Weiteres zweites Emissionsspektrum

56

erster spektraler Transmissionsbereich

58

Abbildungslinse

59

Weitere Abbildungslinse

60

Weiterer zweiter spektraler Transmissionsbereich

62

Weitere Bilderfassungssensorik

64

Weiterer Spektralfilter

66

Blickrichtung

68

Steuereinheit

70

Medizinisches Bildgebungsgerät

72

Endoskop

74

Anzeigeeinheit

76

Anzeigegerät

78

Lichtleiter

80

Beleuchtungsgerät

82

Steuergerät

84

Distaler Abschnitt

86

Proximaler Abschnitt

88

Zwischenabschnitt

90

Verbindungseinheit

92

Schafft

94

Handhabe

96

Bilderfassungsoptikeinheit

98

Strahlteiler

100

Eingangsstrahlengang

102

Optik

104

Strahlengang

106

Strahlengang

108

Haupterstreckungsebene des Spektralfilters

112

Haupterstreckungsebene der Bilderfassungssensorik

116

Diagramm

118

Abszissenachse

120

Minimalwert der Abszissenachse

122

Maximalwert der Abszissenachse

124

Ordinatenachse

126

Minimalwert der Ordinatenachse

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Maximalwert der Ordinatenachse

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Diagramm

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Abszissenachse

134

Minimalwert der Abszissenachse

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Maximalwert der Abszissenachse

138

Ordinatenachse

140

Minimalwert der Ordinatenachse

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Maximalwert der Ordinatenachse

144

Haupterstreckungsebene der weiteren Bilderfassungssensorik

146

Haupterstreckungsebene des weiteren Spektralfilters

148

Peak

160

Diagramm

162

Abszissenachse

164

Minimalwert der Abszissenachse

166

Maximalwert der Abszissenachse

168

Ordinatenachse

170

Minimalwert der Ordinatenachse

172

Maximalwert der Ordinatenachse

174

Weitere erste Filterkante

176

Weitere erste Zentralwellenlänge

178

Weitere weitere erste Filterkante

180

Weitere erste Bandbreite

182

Diagramm

184

Abszissenachse

186

Minimalwert der Abszissenachse

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Maximalwert der Abszissenachse

190

Ordinatenachse

192

Minimalwert der Ordinatenachse

194

Maximalwert der Ordinatenachse

196

Weitere zweite Filterkante

198

Weitere zweite Zentralwellenlänge

200

Weitere zweite Filterkante

202

Weitere zweite Bandbreite

204

Weiteres erstes Beleuchtungsspektrum

206

Peak

208

Weiteres erstes Absorptionsspektrum

210

Weiteres zweites Beleuchtungsspektrum

212

Peak

214

Weiteres zweites Absorptionsspektrum

218

Verfahrensschritt

220

Verfahrensteilschritt

222

Verfahrensteilschritt

224

Verfahrensteilschritt

226

Verfahrensteilschritt

228

Bildgebungsfunktion

230

Verfahrensschritt

In order to eliminate a chromatic imaging error, the control unit 68 switches to activate or deactivate a switching state of the switchable imaging lenses 58a, 59a depending on at least one operating state of the spectral filters 18, 64. This is done synchronized with the control of the lighting, the spectral filter 18a. 64a and/or the image capture sensors 12a, 62a in respective operating modes, so that this process can be part of one of the method steps 220, 222, 224, 226 (cf. 11 ).

10

Image capture unit

12

Image capture sensors

13

Additional image capture sensors

15

Another image sensor

14

Image sensor

16

Filter unit

18

Spectral filter

20

Direction of view

22

First spectral transmission range

24

Second spectral transmission range

26

First filter edge

27

Another first filter edge

28

Second filter edge

29

Another second filter edge

30

First central wavelength

32

Second central wavelength

34

First bandwidth

36

Second bandwidth

38

Interference filter

40

camp

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camp

42

Actor

43

Another actor

44

Lighting unit

46

First lighting spectrum

47

Second lighting spectrum

48

Absorption spectrum

52

Emission spectrum

54

Another first emission spectrum

55

Further second emission spectrum

56

first spectral transmission range

58

imaging lens

59

More imaging lens

60

Further second spectral transmission range

62

Additional image capture sensors

64

Another spectral filter

66

Direction of view

68

Control unit

70

Medical imaging device

72

endoscope

74

Display unit

76

Display device

78

light guide

80

lighting device

82

Control unit

84

Distal section

86

Proximal section

88

Intermediate section

90

Connection unit

92

Creates

94

Handle

96

Image capture optical unit

98

Beam splitter

100

Input beam path

102

optics

104

beam path

106

beam path

108

Main extension plane of the spectral filter

112

Main extension level of the image capture sensor system

116

diagram

118

Abscissa axis

120

Minimum value of the abscissa axis

122

Maximum value of the abscissa axis

124

ordinate axis

126

Minimum value of the ordinate axis

128

Maximum value of the ordinate axis

130

diagram

132

Abscissa axis

134

Minimum value of the abscissa axis

136

Maximum value of the abscissa axis

138

ordinate axis

140

Minimum value of the ordinate axis

142

Maximum value of the ordinate axis

144

Main extension level of the further image capture sensors

146

Main extension plane of the further spectral filter

148

Peak

160

diagram

162

Abscissa axis

164

Minimum value of the abscissa axis

166

Maximum value of the abscissa axis

168

ordinate axis

170

Minimum value of the ordinate axis

172

Maximum value of the ordinate axis

174

Another first filter edge

176

Another first central wavelength

178

More more first filter edge

180

More first bandwidth

182

diagram

184

Abscissa axis

186

Minimum value of the abscissa axis

188

Maximum value of the abscissa axis

190

ordinate axis

192

Minimum value of the ordinate axis

194

Maximum value of the ordinate axis

196

Another second filter edge

198

Another second central wavelength

200

Another second filter edge

202

More second bandwidth

204

Another first lighting spectrum

206

Peak

208

Another first absorption spectrum

210

Further second lighting spectrum

212

Peak

214

Further second absorption spectrum

218

Procedural step

220

Sub-step of the process

222

Sub-step of the process

224

Sub-step of the process

226

Sub-step of the process

228

Imaging function

230

Procedural step

Claims (19)

Medical imaging device, in particular endoscopic imaging device, with at least one image capture unit (10), which has at least one image capture sensor system (12) and at least one optical filter unit (16), which has at least one spectral filter (18), which is designed as an interference filter (38), comprises, which is assigned to the image capture sensor system (12) and is arranged in front of the image capture sensor system (12) when viewed in the viewing direction (20), wherein the spectral filter (18) in a first operating state is designed to provide light according to a first spectral transmission range (22). Image capture sensor system (12) and in a second operating state is designed to transmit light according to a second spectral transmission range (24), which is at least partially different from the first spectral transmission range (22), to the image capture sensor system (12) and the image capture unit ( 10) comprises at least one bearing (40) designed as a tilting bearing, which is designed to store the spectral filter (18) so that it can be transferred from the first operating state to the second operating state and / or vice versa, and with at least one lighting unit (44), which is used for Illumination of an object to be captured by the image capture unit (10) is designed, wherein the illumination unit (44) is designed to provide at least a first illumination light according to an illumination spectrum (46) which lies at least to a large extent outside the first spectral transmission range (22). , wherein the illumination spectrum (46) corresponds at least to a large extent to an absorption spectrum (48) of a spontaneously light-emitting material of the object to be illuminated, wherein an emission spectrum (52) of a spontaneously light-emitting material illuminated by means of the lighting unit (44) is at least to a large extent in first spectral transmission range (22) and wherein the lighting unit (44) is designed to provide at least a second illumination light with an illumination spectrum (47), namely white light, which lies at least to a large extent in the second spectral transmission range (24). Medical imaging device according to Claim 1 , characterized in that the first operating state is defined as a first position of the spectral filter (18) relative to the image capture sensor system (12) and / or the second operating state is defined as a second position of the spectral filter (18) relative to the image capture sensor system (12). Medical imaging device according to Claim 1 or 2 , characterized in that the first spectral transmission range (22) has a first filter edge (26) and the second spectral transmission range (24) has a second filter edge (28), which is spectrally shifted relative to the first filter edge (26). Medical imaging device according to one of the preceding claims, characterized in that the first spectral transmission range (22) has a first central wavelength (30) and the second spectral transmission range (24) has a second central wavelength (32), which is spectrally relative to the first central wavelength (30). is shifted. Medical imaging device according to one of the preceding claims, characterized in that the first spectral transmission range (22) has a first bandwidth (34) and the second spectral transmission range (24) has a second bandwidth (36), which is at least a large part of the first bandwidth ( 34) corresponds. Medical imaging device according to one of the preceding claims, characterized in that the image capture unit comprises at least one actuator (42) which is designed to transfer the spectral filter (18) from the first operating state to the second operating state and/or vice versa. Medical imaging device according to Claim 6 , characterized in that the actuator (42) is designed to transfer the spectral filter (18) from the first operating state to the second operating state of the spectral filter and/or vice versa at least 15 times per second. Medical imaging device according to one of the preceding claims, characterized in that a further emission spectrum (54) of a further spontaneously light-emitting material illuminated by means of the lighting unit (44) lies at least to a large extent outside a first spectral transmission range (56). Medical imaging device according to Claim 8 , characterized in that a further emission spectrum (58) of a further spontaneously light-emitting material illuminated by means of the lighting unit (44) lies at least to a large extent within the second spectral transmission range (60). Medical imaging device according to one of the preceding claims, characterized in that the filter unit (16) comprises at least one switchable imaging lens (58, 59), which is arranged between the spectral filter (18, 64) and the image capture sensor system (12, 62) and which is designed for this purpose , depending on an operating state of the spectral filter (18, 64), to image a transmission spectrum transmitted by the spectral filter (18, 64) onto the image capture sensor system (12, 62). Medical imaging device according to one of the preceding claims, characterized in that the filter unit (16) has at least one further spectral filter (64), which is designed to transmit light in accordance with a further first spectral transmission range (56) in a further first operating state and in a further second operating state is designed to transmit light according to a further second spectral transmission range (60). Medical imaging device according to Claim 11 , characterized in that at least one of the further transmission regions (56, 60) of the further spectral filter (64) is different from at least one transmission region (22, 24) of the transmission regions (22, 24) of the further spectral filter (64). Medical imaging device according to Claim 11 or 12 , characterized in that the image capture unit (10) comprises at least one further image capture sensor system (13), which is assigned to the further spectral filter (64) and is arranged in front of it when viewed in the viewing direction (66) of the further image capture sensor system (13). Medical imaging device according to one of the preceding claims, characterized by at least one control unit (68) which is designed to control at least the image capture unit (10). Medical imaging device according to Claim 14 , characterized in that the control unit (68) is designed to, depending on at least one operating state, at least one spectral filter (18, 64) of the filter unit (16) to activate or deactivate at least one image capture sensor (12). Medical imaging device according to Claim 14 or 15 , characterized in that the control unit (68) is designed to activate or deactivate at least one illumination light according to at least one illumination spectrum of the illumination unit (44) depending on at least one operating state of at least one spectral filter (18, 64) of the filter unit (16). . Medical imaging device according to one of the Claims 14 until 16 , characterized in that the control unit (68) is designed to activate or deactivate a switching state of the switchable imaging lens (58, 59) depending on at least one operating state of at least one spectral filter (18, 64). Medical imaging device according to one of the preceding claims, characterized in that it at least partially forms a medical imaging device, in particular an endoscopic imaging device. Method for operating a medical imaging device, in particular an endoscopic imaging device, preferably according to one of Claims 1 until 18 , in which at least one spectral filter (18), which is designed as an interference filter (38), is assigned to an optical filter unit (16) of an image capture sensor system (12) and is arranged in front of the image capture sensor system (12) when viewed in the viewing direction (20), whereby in at least one method step the spectral filter (18) transmits light in accordance with a first spectral transmission range (22) to the image capture sensor system (12) in at least a first operating state and in a further method step the spectral filter (18) transmits light in accordance with a second spectral transmission range in at least one second operating state (24), which is at least partially different from the first spectral transmission range (22), is transmitted to the image capture sensor system (12) and a bearing (40) designed as a tilt bearing moves the spectral filter (18) from the first operating state to the second operating state and/or vice versa is transferred and at least one illumination unit (44) illuminates an object to be detected with at least one first illumination light according to an illumination spectrum (46), which lies at least to a large extent outside the first spectral transmission range (22), the illumination spectrum (46) being at least one The majority corresponds to an absorption spectrum (48) of a spontaneously light-emitting material of the object to be illuminated, wherein an emission spectrum (52) of a spontaneously light-emitting material illuminated by means of the lighting unit (44) lies at least to a large extent in the first spectral transmission range (22) and wherein the Illumination unit (44) illuminates the object to be detected with a second illumination light with an illumination spectrum (47), namely white light, which lies at least to a large extent in the second spectral transmission range (24).

Images