Endoscopes, disposable endoscope systems, and endoscope light sources

Abstract

The present invention generally relates to endoscopes and endoscope systems, and in particular to disposable endoscopes and / or disposable endoscope systems. In another aspect, the present invention also relates to a light source for an endoscope and / or an endoscope system, for example a light source for a disposable endoscope and / or a disposable endoscope system.

Description

Technical Field

[0001] The present invention generally relates to endoscopes and endoscope systems, and in particular to disposable endoscopes and / or disposable endoscope systems. In another aspect, the present invention also relates to a light source for an endoscope and / or an endoscope system, for example a light source for a disposable endoscope and / or a disposable endoscope system. Background Art

[0002] Diagnostic, surgical, and / or therapeutic instruments, such as endoscopes for diagnosis, minimally invasive intervention, or therapy, are known in rigid or flexible embodiments and are extensively described in the literature. Disposable endoscopes (also known as "disposable endoscopes") are increasingly common, particularly to prevent contamination by single use in order to increase patient safety during medical examinations, treatments, and / or minimally invasive interventions. For this purpose, existing endoscopes are designed to be reusable in the medical technical sense, i.e., cleanable, disinfectable, and, in particular, autoclavable.

[0003] Nevertheless, due to incorrect use or unfavorable design of the reprocessing of such devices, it occasionally happens that the required bacterial count is not achieved and bacteria are therefore transferred to the patient during the next use. This can be avoided by using such disposable endoscopes.

[0004] Another factor driving the growing use of disposable endoscopes is economic efficiency. In particular, the cost of proper and regular reprocessing after each treatment is very high for practitioners and clinics. Furthermore, the expense of cleaning instruments such as thermal disinfectors, autoclaves, and / or plasma sterilizers is substantial, making the use of disposable endoscopes generally more rational.

[0005] A further advantage is that such a disposable endoscope can be used as a mobile "handheld" instrument and can therefore also be used in emergency medicine, military medical care or in hard-to-reach areas, such as disaster relief missions where reprocessing is not possible.

[0006] The following are examples of such disposable endoscopes, "single-use" endoscopes, or "disposable endoscopes" described in the literature:

[0007] Document US 3581738 A1 discloses a disposable endoscope comprising a main body made of a synthetic resin material having a generally tubular side wall forming the endoscope and an integral elongated light-guiding element embedded in the side wall, wherein the element is formed of a light-guiding material coated with a transparent material having a refractive index different from that of the light-guiding material, wherein the main body is formed of two mating halves separated axially by the endoscope, wherein each half has an element enclosure.

[0008] US Pat. No. 4,964,710 A1 describes a rigid endoscope equipped with an objective lens system, an eyepiece, and an intermediate relay lens. The relay system is a hybrid system using plastic and glass components. The plastic component consists of an even number (N) of axially oriented lenses, each with a length of the same order as their diameter. The glass component is an odd number (N-1) of axially oriented glass oblate cylinders with polished end faces.

[0009] Document EP 1890173 A1 describes a method for manufacturing an optical conductor that can be used in this type of endoscope. In this method, a large number of optical fibers are bundled, and then the optical fiber bundle is cut at a portion of a connector (Mundstück) connected to the middle part of the optical fiber bundle. This separates the optical fiber bundle into a first optical fiber bundle and a second optical fiber bundle. The dividing surfaces of the first optical fiber bundle and the second optical fiber bundle have the same characteristics and conditions because the first optical fiber bundle and the second optical fiber bundle are formed by bundling the same optical fibers. The first optical fiber bundle is assembled in the insertion part of the endoscope, while the second optical fiber bundle is assembled in a flexible hose, so that the first optical conductor is formed in the insertion part of the endoscope, and the second optical conductor is formed in the flexible hose. This creates a separable light transmission path for the optical conductor.

[0010] Such endoscopes are subject to high costs due to their single-use application, necessitating optimized manufacturing costs for their components or parts. One of the key components for imaging and illumination is the light conductor or image conductor. These are currently assembled or processed using relatively complex process steps. The high cost of current light conductors and image conductors is often due to complex mechanical components, sometimes combined with optical elements (such as lenses) containing them, and sometimes also complex processing steps (such as grinding and polishing of the end faces).

[0011] On the other hand, the use of endoscopes, particularly in medical technology, also places certain optical demands on the system. These include directing the light provided by the light source to the examination site with minimal loss, displaying the examination site in true or target colors, and avoiding excessive heating in the examination site. The light flux provided by the light source and its transmission to the distal end of the endoscope present particular challenges. Especially for endoscope systems with small diameters, both extremely bright light sources and light guides with optimized light flux are required.

[0012] When using active electronics (e.g. camera chips and / or LEDs) for illumination, requirements for electrical insulation, electrical shielding, and patient leakage current must also be taken into account. Depending on the endoscope's field of application, maximum limits must not be exceeded. For example, a leakage current of 10 μA is required in cardiac applications, which corresponds to the CF classification (see EN 60601-1, 3rd edition, Table 3).

[0013] In addition to these optical and electrical requirements, biocompatibility requirements must also be taken into account. Regarding biocompatibility, it must be ensured that the material is compatible with human tissue. For medical products that may come into contact with the human body, there are regulatory requirements to identify and evaluate possible interactions and adverse side effects. The choice of the required tests depends on the type and duration of human contact. This type of biological evaluation is always required for products that come into direct contact with patients, in accordance with the European Guideline for Medicinal Products MDD 93 / 42EWG (MDD) or Regulation (EU) 2017 / 745 of April 5, 2017 (MDR).

[0014] The main rules for biological testing and evaluation of materials are DIN EN ISO 10993 and the United States Pharmacopoeia Class VI test (USP Class VI). Although the more popular ISO 10993 was originally intended to replace the USP Class VI test, the USP test is currently more commonly used to evaluate biocompatible plastics. To this end, on the one hand, the chemical compounds of materials used in invasive applications are evaluated, and on the other hand, cytotoxicity tests are carried out, in which possible toxic effects on living cell cultures are examined. The requirements in this regard are outlined in DIN EN ISO 10993, especially in Parts 1 and 5 (DIN EN ISO 10993-1:2010-04). In the United States, this is subject to FDA requirements. The corresponding requirements with respect to DIN EN ISO 10993 are recorded in USP Class VI.

[0015] The design of the endoscope as a disposable endoscope also benefits from the fact that so-called reprocessing methods, i.e. cleaning / sterilization processes using strongly alkaline solutions and autoclaving at temperatures of up to 135° C. and a typical steam pressure of approximately 3 bar, do not have to be considered to the same extent when selecting the material, which in particular also allows for a more economical selection of materials. Only the suitability for gas sterilization methods (e.g. ethylene oxide) and the RoHS and REACH regulations for the material need to be considered.

[0016] Patent applications DE 10 2019 125 912 and DE 10 2018 107 523, owned by the same applicant, deal with various aspects of optical waveguides. Laser-based light sources are not mentioned.

[0017] US patent US 6,398,721B relates to a surgical microscope apparatus which may include a laser diode.

[0018] US patent application US 2006 / 0279950 A1 describes an LED. An endoscope is not mentioned, but a light guide, for example comprising fibers, can be used. The LED is operated in transmission mode.

[0019] US patent application US 2006 / 0152926 A1 also describes an LED which can also be used, for example, in an endoscope.The LED is operated in transmissive mode.

[0020] US Patent No. 5,436,655 A describes an endoscope which may include a laser.

[0021] A highly efficient light source is described in US patent application US 2004 / 0246744 A1.

[0022] An endoscope that can also be operated with a laser is described in US patent application US 2019 / 0014979 A1.

[0023] US patent application US 2019 / 0290100 A1 describes an optical imaging system that can be used, in particular, for fluorescence microscopy (STED microscopy).

[0024] International patent application WO 2013 / 092498 A1 describes an endoscope which may include a laser diode as a light source.

[0025] US patent application US 2006 / 0069314 A1 describes a solid-state light source for an endoscope.

[0026] An optoelectronic device is described in German patent application DE 10 2017 108 698 A1.

[0027] However, the advantages of high-light-density illumination have not been economically realized to date. In particular, the advantages of lasers used in disposable endoscopes have not been realized economically. Summary of the Invention

[0028] The object of the present invention is to at least partially overcome or at least reduce the disadvantages of the prior art and in particular to provide an endoscope system, in particular a single-use endoscope system, comprising a bright light source or an illumination element with high brightness and a light guide system optimized therefor.

[0029] The objects of the invention are achieved by the subject matter of the independent claims. Specific and preferred embodiments are described in the dependent claims.

[0030] The present invention relates to an endoscope comprising a first component and a second component, wherein a light source is integrated into the first component, and wherein the second component has a proximal end connected to the first component, preferably a detachably connected proximal end, and a distal end, wherein an element for capturing or transmitting images and / or capturing or transmitting optical information, such as a camera chip or a fiber optic element, is arranged in the distal end, and wherein an optical fiber having at least one optical fiber extends in the second component to guide light from the light source from the proximal end to the distal end and emit it at the distal end, and preferably a power supply line for feeding the camera chip is arranged (especially when the camera chip is arranged at the distal end), and wherein the light source comprises at least one laser for emitting primary light and a converter that at least partially converts the laser light into light of another wavelength (secondary light) and emits it, wherein the converter is coupled to the proximal end of the second component connected to the first component so that the light converted and emitted by the converter is coupled into the optical fiber. Fiber optic elements for image capture or transmission are also called "image guides" and consist of tens of thousands of individual fibers arranged in an orderly manner relative to one another at their end faces. Such a fiber-optic element can consist in particular of glass or plastic or contain glass or plastic, for example be designed as a glass fiber or a plastic fiber.

[0031] This embodiment of the endoscope has a number of advantages.

[0032] Specifically, according to the present disclosure, the endoscope is divided into two components. A first component, also referred to as a proximal component, houses a light source comprising at least one laser configured to emit primary light. For example, the laser can be configured to emit blue light and / or ultraviolet light. Furthermore, the first component includes a converter configured to at least partially convert the laser light into light of a different wavelength and emit the resulting light.

[0033] This is advantageous because laser light is usable in this way. In particular, it is possible in this way to achieve a particularly high illumination intensity.

[0034] The converter is coupled to the proximal end of the second component connected to the first component, so that the light converted and emitted by the converter is or can be coupled into the optical fiber.

[0035] In other words, the first component is designed such that it can be connected to the second component, which can also be referred to as the distal component, or it is even connected to the second component.

[0036] Depending on the precise design and the type of elements it contains, the first component can be embodied, for example, as a handpiece, i.e., as a component for manually controlling and / or holding an endoscope. However, it is also possible that the first component includes elements for controlling and / or operating the endoscope, for example, also as a control unit and / or an evaluation unit, so that in this case the first component can also be configured as an operating instrument for the endoscope.

[0037] The endoscope further includes a second component having a proximal end and a distal end, wherein an optical fiber including at least one optical fiber extends through the second component. The optical fiber is configured to guide light from a light source from the proximal end to the distal end and emit light at the distal end. An image acquisition component, such as a camera chip or an optical fiber image conductor, is disposed at the distal end. If the distal end includes a camera chip, the second component preferably also includes power supply lines for supplying power to the camera chip.

[0038] Such an embodiment of an endoscope having two components (or also assemblies) is advantageous because, according to the described embodiment, the endoscope is constructed such that the first component comprises relatively more expensive components, such as a light source including at least one laser, while the second component comprises relatively less expensive components. It is possible to separate the endoscope and, in this way, for example, accommodate the less expensive components in a relatively less expensive single-use assembly and a few more expensive components in a multiple-use assembly.

[0039] Thus, for the first time, it is now possible to provide an endoscope that combines the advantages of very high-quality lighting with the advantages of an endoscope that is intended for single use only. It should be noted that the endoscope according to the present disclosure does not necessarily have to be implemented as a disposable endoscope, or at least partially as a disposable endoscope. Rather, it is also conceivable to adjust it as needed.

[0040] Advantageously, the first and second components can be detachably connected to each other. If the endoscope is designed at least partially as a single-use endoscope, the second component can be disposed of after use, for example. However, the second component can also be detachably connected to the first component while still being intended for multiple uses and, after being separated from the first component, undergoing certain cleaning and disinfection processes for medical use.

[0041] The endoscope according to the present disclosure (which can also be described as a modular endoscope) can, on the one hand, also simplify the handling. On the other hand, in particular when the endoscope is designed as a disposable endoscope or at least partially as a disposable endoscope, i.e., an endoscope at least some of whose components are intended for single use only, it is possible to combine high-quality illumination (e.g., by means of laser illumination that enables high light intensity) with the advantages of disposable instruments.

[0042] The second component comprising the optical waveguide can be, for example, rigid or flexible. Generally, the second component can also refer to the so-called endoscope shaft, which, in the context of this disclosure, generally refers to both a rigid second component and a flexible component, such as simply a flexible outer sleeve, e.g., made of plastic material. If the second component is rigid, it can be designed, for example, such that the optical waveguide comprised by the second component is at least partially surrounded by a tube segment or multiple tube segments made of metal or plastic. The exact embodiment of the second component can be selected depending on the preferred field of application of the endoscope.

[0043] According to a preferred embodiment, the converter comprises a ceramic converter material. This embodiment is advantageous in that a particularly high luminous density can be achieved, also for white light. That is, ceramic converter materials are particularly temperature-stable, making it possible to achieve a particularly high brightness. Converters based on organic materials or combinations of organic and ceramic converter materials are also conceivable. In particular, the converter can be designed so that it comprises a converter element, which comprises two or more converter materials, which can in particular be designed so that they convert the primary light into light of different spectral compositions. For example, it is conceivable that the converter element comprises so-called "yellow" and so-called "red" phosphors. Phosphors are understood here to mean luminescent materials. For example, these materials can be present as a mixture, for example as a mixture comprising organic and ceramic materials, or as a mixture of organic or ceramic materials. However, the converter can also be designed so that it comprises a plurality of converter elements, each of which comprises different converter materials. Mixtures are also conceivable in these embodiments.

[0044] In particular, the ceramic converter material can be a luminescent ceramic material or include a luminescent ceramic material. In the context of the present invention, this means that the converter can, for example, consist mainly (i.e. at least 50% by weight) or essentially (i.e. at least 90% by weight) of a luminescent ceramic material. The converter can also consist completely of a luminescent ceramic material. In particular, the converter and / or the converter element comprises a luminescent ceramic material or consists of a luminescent ceramic material. The converter and / or the converter element can also be designed as a composite material, for example as a phosphor-glass composite, or as a phosphor-plastic composite, in particular a phosphor-silicon composite, or as a phosphor-ceramic composite, and in this case preferably contain at least 10% by weight, for example 10% to 30% by weight, in particular 10% to 20% by weight of luminescent ceramic material.

[0045] According to one embodiment, the converter and / or the converter element comprises a garnet-like ceramic material as the luminescent ceramic material or consists predominantly (i.e. at least 50% by weight) or essentially (i.e. at least 90% by weight) or completely thereof, wherein the garnet-like ceramic material preferably has the following formula:

[0046] A3B5O 12 :RE, where

[0047] A contains Y and / or Gd and / or Lu, and

[0048] B contains Al and / or Ga,

[0049] And wherein RE is selected from the group of rare earth elements, and preferably comprises Ce and / or Pr.

[0050] According to yet another embodiment, the garnet-like ceramic material has the following formula:

[0051] (Y 1-x Ce x )3Al5O 12 , and / or

[0052] (Y 1-x-y Gd y Ce x )3Al5O 12 , and / or

[0053] (Lu 1-x Ce x )3Al5O 12 , and / or

[0054] (Y 1-x-z Lu z Ce x )3Al5O 12 ,

[0055] For x: 0.005 <x<0.05,

[0056] And where for y: 0 <y<0.2,

[0057] And where for z: 0 <z<1。

[0058] According to one embodiment, the converter and / or the converter element comprises a luminescent ceramic material or consists predominantly (i.e. at least 50% by weight) or essentially (i.e. at least 90% by weight) or completely thereof, wherein the converter exhibits:

[0059] - single-phase solid ceramics (so-called light ceramics), and / or

[0060] - multiphase solid ceramics, and / or

[0061] - single-phase or multi-phase ceramics of specific porosity, and / or

[0062] - Composite materials, such as phosphor in glass (PIG) ​​and / or phosphor in silicone (PIS).

[0063] According to another embodiment, the ceramic material also comprises other oxides (except garnet compounds) and nitrides, in particular selected from the group of aluminum oxynitride and silicon aluminum oxynitride.

[0064] According to another embodiment, the converter and / or converter element is designed as a porous sintered ceramic with a porosity of between 0.5% and 10%, preferably between 4% and 8%. The porosity is related to the volume. The average pore diameter is preferably between 400 μm and 1200 μm, more preferably between 600 μm and 1000 μm, and particularly preferably between 600 μm and 800 μm.

[0065] In the context of the present disclosure, single-phase ceramics (or optical ceramics) refer to ceramics in which at least 95% by volume of the crystals and / or crystallites comprise a homomorphic phase. Preferably, the volume content of heteromorphic phases is significantly lower. In particular, even more than 96% by volume, more than 97% by volume, more than 98% by volume, or even more than 99% by volume of the crystals and / or crystallites comprised by the ceramic can be configured as a homomorphic phase. In addition, it is not excluded that single-phase ceramics can also comprise amorphous components. However, these amorphous components are generally less than 5% by volume.

[0066] It is particularly advantageous if the ceramic material can be designed such that it has a thermal conductivity in the range of 1 W / mK to 20 W / mK. In this way, the thermal energy generated or formed during the conversion can be distributed particularly well, so that the conversion properties of the converter material change only slightly or even not at all during operation of the material.

[0067] In particular, the ceramic converter material can be of polycrystalline design.

[0068] It is particularly advantageous if the material is homogeneous or substantially homogeneous, wherein a homogeneous embodiment of the material preferably means that the material is a single-phase ceramic (or photoceramic).

[0069] According to another embodiment, the converter comprises at least two ceramic converter materials that convert the laser light into light with different spectral compositions. This embodiment is particularly advantageous when particularly precise and / or detailed examinations are required to determine the condition of an object or area to be examined, particularly in the medical field where precise information regarding the condition of the tissue to be examined is required, for example, for the targeted creation of treatment and / or therapy plans. This is because this method enables high illumination intensity, light with a color composition that deviates from the "white" color position, and / or the spectral composition of the light to be adapted to the specific situation.

[0070] Particularly advantageously, the converter comprises two converter elements, each of which contains a ceramic converter material, so that the converter elements convert the light into light with different spectral compositions. This makes it particularly easy to adapt the color position, especially in this embodiment, by appropriately controlling the illumination of only one of the two converter materials and / or distributing the laser light accordingly over both converter materials.

[0071] According to one embodiment, the converter is optically coupled to the optical waveguide such that light diffusely reflected by the converter is coupled, or at least can be coupled, into the optical waveguide. This helps ensure that straight light with the desired spectral distribution is guided through the optical waveguide to the area to be examined by the endoscope. In the context of this disclosure, unless explicitly stated otherwise, diffusely reflected light refers to light converted and / or scattered and / or reflected by the converter.

[0072] According to another preferred embodiment, the laser is arranged and directed toward the converter such that only light converted and / or scattered and / or reflected by the converter is coupled into the optical waveguide, wherein this light can also contain, for example, a portion of the scattered or reflected primary light.

[0073] From a safety point of view, this embodiment of the endoscope is particularly advantageous in that it prevents the laser from reaching the area to be inspected.

[0074] Generally, it is possible to arrange the converter and the laser in a so-called transmissive configuration, i.e., the laser light passes through (i.e., transmits through) the converter and is converted and / or scattered there. However, it is also possible and even preferred, in particular to ensure that no laser light (i.e., light emitted by the laser but not converted and / or scattered) reaches the area to be inspected, to arrange the converter and the laser in a reflective configuration, i.e., the laser light impinges on the converter and is reflected by it, and is converted and / or scattered there.

[0075] According to another embodiment, the laser is arranged such that the laser light is directed to the converter and / or can be redirected thereto substantially in the opposite direction to the direction of emission of the light converted and / or scattered and / or reflected by the converter and coupled into the optical waveguide. From a safety perspective, this embodiment can be particularly advantageous for preventing direct laser light coupling into the optical waveguide. Such an embodiment of the endoscope can be achieved, for example, by including a mechanism for directing the laser light in the opposite direction to the direction of emission of the diffusely reflected light from the converter. For example, this mechanism can be and / or include an optical fiber.

[0076] Here, “substantially opposite to the light emission direction of the light converted by the converter and coupled into the optical waveguide” means that the surface of the converter and / or converter element and / or the normal vector on the converter element forms an angle of at least ±10° with the coupling direction of the primary light.

[0077] Suitable optical fibers for such endoscope systems may include, for example, tens, hundreds, or even thousands of individual fibers. The exact number of individual fibers in the optical fiber depends, for example, on the final diameter of the optical fiber and / or the diameter of the individual fibers it comprises. Common fiber diameters are between 20 μm and 100 μm. Typical diameters are 30 μm, 50 μm, and 70 μm.

[0078] In particular, for disposable endoscopes or small-sized endoscope systems, it is advantageous to use a few thick fibers as optical fibers to ensure sufficient light density or illumination intensity in the area to be inspected. This allows for quick and cost-effective assembly while ensuring a high light flux from the laser light source to the distal end of the endoscope.

[0079] A maximum of twenty, preferably ten, such individual fibers has been found to offer a good compromise between assembly effort and sufficient light transmission, with one fiber being sufficient for ultra-thin endoscope systems. Fiber bundles of three or seven individual fibers offer the advantage that they can be very tightly packed in a common sleeve. A particular advantage of a seven-fiber arrangement is that the individual fibers can be more easily arranged in a circular pattern in a common sleeve, resulting in an ideal packing density for fibers with a circular cross-section. This seven-fiber arrangement allows the individual fibers to be grouped around a camera chip or image conductor, for example, at the distal end of an endoscope, to uniformly illuminate the tissue being examined. For the more common square chip shapes of lasers, light-emitting diodes, or converters as light sources, it may also be advantageous to use four individual fibers, or integer multiples of four or two such fibers. This allows the cavity available for illumination to be filled with more fibers in terms of the maximum possible active fiber area (i.e., the actual fiber-optic cross-sectional area), while also enabling greater light incoupling.

[0080] It is advantageous if the optical fiber or optical fibers have a diameter in the range of 100 μm to 1000 μm, preferably to 600 μm, preferably in the range of 150 μm to 400 μm. Such fibers can be assembled much more easily than individual fibers and still have a sufficiently small minimum bending radius. For today's optical fibers with a diameter of 1x1 mm 2For endoscopes with large and small camera chips, four individual fibers, one on each side of the camera, with diameters ranging from 200 μm to 300 μm, are ideal. Similarly preferred are arrangements with a total of eight or twelve individual fibers, with two or three fibers on each side of the camera. In this case, the diameters of the individual fibers range from 150 μm to a maximum of 200 μm. Provision can also be made, for example, to use fibers with different diameters to maximize the area or available space between the camera chip and the surrounding sheath, thereby achieving the highest possible light throughput. In an arrangement of twelve fibers, three fibers are arranged on each side of the camera, with the central fiber having a diameter of, for example, approximately 250 μm, while the other two fibers have diameters of only 100 μm to 150 μm.

[0081] In principle, it is also possible to use fine fiber bundles instead of individual fibers, which consist in particular of very fine individual fibers, preferably with an individual fiber diameter of less than 70 μm, particularly preferably less than 50 μm, typically 30 μm, and which have only a very thin outer jacket that holds the fiber bundle together. The present applicant has described such a fiber bundle embodiment in further applications that have not yet been published.

[0082] According to a further embodiment, the optical fiber or fibers are step-index glass fibers. Preferably, the optical fiber or fibers are step-index glass fibers, the glass composition of which, apart from unavoidable traces, contains no lead and / or other heavy metals, no antimony and / or arsenic and / or other critical elements such as Cr(VI).

[0083] In the context of the present disclosure, a fiber is an object whose maximum transverse dimension in one spatial direction of a Cartesian coordinate system is at least 10 times greater, preferably at least 50 times greater, than its maximum transverse dimensions in two other spatial directions perpendicular to the first spatial direction. In other words, a fiber is an extremely long and thin object.

[0084] In the context of this disclosure, a step-index glass fiber refers to a glass fiber whose refractive index changes from the inner (core) to the outer portion in at least one step. In this case, the glass fiber comprises core glass and cladding glass, wherein the core glass and the cladding glass have different refractive indices.

[0085] Glass fibers contain glass. In addition to the glass material, they may also contain another material at least partially surrounding the surface of the glass material, a so-called coating. Depending on the intended use, different glassy materials can be used for glass fibers. In particular, glass fibers can contain single-component and / or multi-component glass. For example, glass fibers may contain quartz glass as the primary single-component glass and / or, in particular, be configured as quartz glass fibers. The quartz glass may also be doped, for example, with OH ions and / or fluorine, and / or, for example, in water-rich or water-depleted quartz glass variants, in which case it is still referred to as single-component glass, or may contain multi-component glass, such as multi-component silicate glass. Furthermore, the glass may also be configured as chalcogenide glass. Quartz glass fibers or quartz fibers also refer to fibers containing doped quartz glass.

[0086] Preferably, the optical fiber comprises a fiber core and a fiber side or fiber cladding. In a preferred embodiment, the core layer is made of core glass.

[0087] Preferably, the optical fiber comprises a fiber cladding surrounding a fiber core. In a preferred embodiment, the fiber cladding comprises cladding glass.

[0088] The halogen or halide content of the fiber cladding is preferably less than 500 ppm (m / m), more preferably less than 400 ppm (m / m), more preferably less than 300 ppm (m / m), more preferably less than 250 ppm (m / m), more preferably less than 200 ppm (m / m), more preferably less than 150 ppm (m / m), more preferably less than 100 ppm (m / m), more preferably less than 80 ppm (m / m), more preferably less than 60 ppm (m / m), more preferably less than 40 ppm (m / m), more preferably less than 20 ppm (m / m), and even more preferably less than 10 ppm (m / m). In particularly preferred embodiments, the fiber cladding is halogen-free. Halogens are, for example, chlorine, fluorine, bromine, and / or iodine, or their anions. Excessive halogen concentrations in the fiber cladding can lead to the formation of corresponding halogen acids, particularly during steam sterilization. These halogen acids can reduce the resistance of the optical fiber product and leak therefrom. In particular, halogen acids can attack materials such as stainless steel in autoclaves and endoscopes, leading to undesirable rust formation.

[0089] The halogen or halide content of the fiber core is preferably less than 500 ppm (m / m), more preferably less than 400 ppm (m / m), more preferably less than 300 ppm (m / m), more preferably less than 250 ppm (m / m), more preferably less than 200 ppm (m / m), more preferably less than 150 ppm (m / m), more preferably less than 100 ppm (m / m), more preferably less than 80 ppm (m / m), more preferably less than 60 ppm (m / m), more preferably less than 40 ppm (m / m), more preferably less than 20 ppm (m / m), and even more preferably less than 10 ppm (m / m). In a particularly preferred embodiment, the core layer is halogen-free. Halogens according to the present invention are, for example, chlorine, fluorine, bromine, and / or iodine, or their anions. Excessive halogen concentrations in the fiber core can lead to the formation of corresponding halogen acids, particularly during steam sterilization. These halogen acids can reduce the resistance of the optical fiber product and leak therefrom. In particular, halogen acids can attack the materials of autoclaves and endoscopes, such as stainless steel, and lead to undesirable rust formation.

[0090] In certain embodiments, the optical fiber is a silica fiber. In one embodiment, the silica content of the fiber cladding and / or the fiber core is at least 76% by weight, more preferably at least 81% by weight, more preferably at least 84% by weight, more preferably at least 88% by weight, more preferably at least 92% by weight, more preferably at least 95% by weight, more preferably at least 97% by weight, and more preferably at least 98% by weight. A higher silica content results in increased chemical resistance and increased thermal resistance.

[0091] In one embodiment, the core glass has the following characteristics:

[0092] The core glass preferably contains at least 8% by weight of SiO2, more preferably at least 23% by weight, more preferably at least 24% by weight, particularly preferably at least 25% by weight, or even at least 26% by weight. In a specific embodiment, the core glass may contain even at least 28.3% by weight of SiO2, particularly preferably at least 34% by weight of SiO2. In some preferred embodiments, the core glass contains even at least 35% by weight of SiO2, more preferably at least 42% by weight of SiO2.

[0093] The preferred core glass of the present invention comprises the following components in the following composition ranges by weight percentage:

[0094] Components Lower limit Upper limit <![CDATA[B2O3]]> 0 24 <![CDATA[SiO2]]> 23 62.1 <![CDATA[Al2O3]]> 0 10 <![CDATA[Li2O]]> 0 10 <![CDATA[Na2O]]> 0 18.5 <![CDATA[K2O]]> 0 25.7 BaO 0 57.8 ZnO 0 40 <![CDATA[La2O3]]> 0 25 <![CDATA[ZrO2]]> 0 10 <![CDATA[HfO2]]> 0 14.2 <![CDATA[SnO2]]> >0 2 MgO 0 8 CaO 0 8 SrO 0 24.4 <![CDATA[Ta2O5]]> 0 22 <![CDATA[Y2O3]]> 0 11.9 <![CDATA[Rb2O]]> 0 15 <![CDATA[Cs2O]]> 0 21 <![CDATA[GeO2]]> 0 7.5 F 0 2 <![CDATA[ΣR2O]]> 5 20 ΣMgO, CaO, SrO, ZnO 20 42

[0095] R2O is the sum of all alkali metal oxide contents.

[0096] The core glass may include one or more of the following components: Cs2O, Rb2O, MgO, CaO, SrO, Gd2O3, Lu2O3, Sc2O3, Y2O3, In2O3, Ga2O3 and WO3.

[0097] Unless otherwise specified herein, the following components are preferably not included in the core glass, or their concentrations are limited to only up to 500 ppm, due to unavoidable raw material impurities: TiO2, CeO2, Nb2O5, MoO3, Bi2O3, PbO, CdO, Tl2O, As2O3, Sb2O3, SO3, SeO2, TeO2, BeO, radioactive elements, and coloring components. TiO2 should be avoided in particular, as it can strongly absorb in the UV range. In a preferred embodiment, the component WO3 should also be avoided.

[0098] The core glass may contain the components TiO 2 , CeO 2 , Nb 2 O 5 and / or Bi 2 O 3 in an amount of up to 0.5% by weight, preferably up to 0.3% by weight, and particularly preferably up to 0.2% by weight. In a preferred embodiment, the glass core does not contain these components.

[0099] Preferably, the core glass contains no optically active components, in particular Sm2O3, Nd2O3, Dy2O3, Pr2O3, Eu2O3, Yb2O3, Tb2O3, Er2O3, Tm2O3 and / or Ho2O3. CeO2 absorbs in the UV range, so that the preferred glass core contains no CeO2.

[0100] In particular, for core glasses with a refractive index greater than 1.65, the total content of the alkaline earth metal oxide components La2O3, Ta2O5, ZrO2, and HfO2 is preferably at least 40% by weight, more preferably at least 42% by weight, even more preferably at least 50% by weight, and particularly preferably at least 55% by weight. If the content of these components is too low, the preferred refractive index is generally not achieved. Depending on the formulation, this total content should not exceed 72% by weight.

[0101] In one embodiment, the cladding glass has the following characteristics: the SiO2 content of the cladding glass is preferably >60% by weight, more preferably >65% by weight, and particularly preferably at least 69% by weight. The SiO2 content is preferably up to 75% by weight, particularly preferably up to 73% by weight. Cladding glass tends to be more susceptible to environmental influences than core glass. A higher SiO2 content provides better chemical resistance. Therefore, the content of this component in the cladding glass is preferably greater than that in the core glass.

[0102] Preferably, the composition of the cladding glass is selected or matched to the core glass so that the difference between the linear thermal expansion coefficient of the cladding glass and the linear thermal expansion coefficient of the core glass is as small as possible. In general, the coefficient of thermal expansion (CTE) of the fiber core and the fiber cladding can be the same or different in the temperature range of 20°C to 300°C. In particular, the CTE is different. The CTE of the cladding is preferably smaller than the CTE of the fiber core, typically at least 1.0*10 -6 / K, but depending on the glass, it can also be usually smaller than at least 2.5*10 -6 / K. The CTE of the fiber core is usually 6.5*10 -6 / K to 10*10 -6 / K, the CTE of the cladding is 4.5*10 -6 / K to 6*10 -6 / K. This ensures that the fiber core contracts more than the fiber cladding during cooling, so that a compressive stress is built up in the fiber cladding that protects the fiber, which is beneficial to the mechanical load-bearing capacity of the fiber, in particular its bending strength.

[0103] The following table shows some preferred compositions of cladding glass that can be used with the core glass. The cladding glass comprises (oxides in wt. %):

[0104] oxides Group 1 Group 2 Group 3 Group 4 <![CDATA[SiO2]]> 70-78 63-75 75-85 62-70 <![CDATA[Al2O3]]> 5-10 1-7 1-5 1-10 <![CDATA[B2O3]]> 5-14 0-3 10-14 >15 <![CDATA[Li2O]]> none 0–1 0–3 <0.1 <![CDATA[Na2O]]> 0-10 8-20 2-8 0-10 <![CDATA[K2O]]> 0-10 0-6 0-1 0-10 MgO 0-1 0-5 none 0-5 CaO 0-2 1-9 none 0-5 SrO 0-1 none none 0-5 BaO 0-1 0-5 none 0-5 halogen none none none none

[0105] In another embodiment, the core glass and / or the cladding glass is a chalcogenide glass, which can be used particularly in the infrared range. The following table shows the preferred compositions of the chalcogenide core glass and / or the chalcogenide cladding glass in terms of molar percentages:

[0106] Components mol..% S 50-90 Ga 0-25 As 0-40 Ge 0-35 <![CDATA[R 1 (R 1 Hal form added)]]> 0-7.25 <![CDATA[R 2 (R 2 Hal form added)]]> 0-13.5 <![CDATA[M 1 (With M 1 Hal2 form added)]]> 0-5 <![CDATA[M 2 (With M 2 Hal2 form added)]]> 0-7.25 <![CDATA[Ln (added in the form of LnHal3)]]> 0-4 The sum of Ga, As and Ge 10-42 <![CDATA[R 1 、R 2 、M 1 、M 2 and the sum of Ln]]> 0-16 The sum of Hal 0-16

[0107] Here, Hal=F, Cl, Br and / or I; Hal2 and / or Hal3=Cl and / or Br; R 1 =Li, Na, K, Rb and / or Cs; R 2 =Ag and / or Cu; M 1 =Mg, Ca, Sr and / or Ba; M 2 = Zn, Cd, Hg and / or Pb; Ln = La, Ce, Pr, Nd, Pm, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm, Ty, Lu, Y and Sc.

[0108] It is particularly advantageous if the glass fibers, fiber rods or pressed fiber rods consist of lead-free or heavy metal-free core glass and cladding glass. Such fiber systems offer high transmittance in particular in the VIS spectral range and, due to the relatively high transmittance in the blue spectral range, a high degree of color fidelity, which is particularly important in the medical evaluation of tissues. Often, only slight differences in the color of tissue determine whether it is a benign or malignant tissue change. Therefore, a high CRI value for the entire system consisting of light source, light conductor and imaging device is very important, wherein the CRI (color rendering index) is a characteristic factor of the photometric parameter, which is used to describe the color rendering quality of light sources with the same correlated color temperature. CRI values ​​of more than 90 can be achieved with the above-mentioned glass fibers, fiber rods or pressed fiber rods. The applicant is SCHOTT The product of ® discloses such a fiber system and its composition can be found in DE 102012100233 B4 and DE 102013208838 B4. EP 2072477 B1 also describes a similar lead-free fiber system.

[0109] Especially for use in endoscopy, it is advantageous if the glass fiber, fiber rod, or pressed fiber rod consists of a glass system whose acceptance angle 2α for the conducted light is greater than 80°, particularly preferably greater than 100°, corresponding to a numerical aperture (NA) greater than 0.64, particularly preferably greater than 0.77. On the one hand, this allows light from an LED, which typically has a very wide radiation angle, to be coupled into the glass fiber, fiber rod, or pressed fiber rod without requiring complex optics at the proximal end and without increasing coupling losses. On the other hand, wide-angle illumination can be achieved at the distal end without requiring additional optics, which is particularly advantageous for endoscopic examinations. If the glass fiber, fiber rod, or pressed fiber rod has an acceptance angle 2α of at least 120° or an NA of at least 0.86, optimal illumination is achieved with currently common camera viewing angles (typically 120° diagonally).

[0110] As mentioned above, after the drawing process, glass fibers typically have a flawless, flame-polished surface that needs to be protected as much as possible from damage. For this purpose, so-called coatings are applied to the glass fibers before the winding process. These coatings protect the fibers, in particular, when they rub against each other and when they come into contact with, for example, metal surfaces. These coatings typically consist of wax- or stearin-based solutions that are sprayed onto the glass fibers. Such coatings are further described in the applicant's previously unpublished applications.

[0111] With regard to further mechanical stability of the fibers, especially in the case of fibers with larger diameters as described above, it has proven advantageous if one or more optical fibers have a polymer-based coating or jacket at least partially and / or partially arranged on their outer surface, which is made of a polymer-based tubing, for example, in the form of a shrink tubing. This allows for fibers with increased strength and, therefore, a smaller bending radius. This measure significantly reduces or compensates for the inherent disadvantages of thicker fibers with regard to increased stiffness and minimized permissible bending radius.

[0112] According to one embodiment, the optical fiber comprises a plurality of optical fibers, wherein at least one optical fiber, preferably a plurality of optical fibers, particularly preferably all optical fibers have a polymer-based coating or a sheathing made of a polymer-based tube arranged at least partially and / or regionally on their side surface.

[0113] Advantageous coatings are those based on acrylates, polyamides, polyurethanes, polyimides, epoxies, ethylene-tetrafluoroethylene copolymers or polyxylene compounds (also known as polyxylene coatings), for example based on polyparaxylene compounds, for example under the name "Parylene", or mixtures of these compounds. Suitable coating materials are for example known by the names or trade names or the names (polyamide) or or The coating is commercially available from polymethyl methacrylate (PMMA) or polymethyl methacrylate (PMMA) as a coating or coating material. These layers are typically cured by heat or with the aid of UV light. Alternatively or additionally, the coating may also contain a thermoplastic elastomer, such as a thermoplastic polyester elastomer or a thermoplastic copolyester elastomer (for example, commercially available under the name Hytrel), or silicone.

[0114] In special cases, metal coatings, for example made of gold or aluminum, can also be used.

[0115] It is particularly advantageous that such a coating can be applied or applied to one or more optical fibers immediately after stretching the fibers by dipping, spraying, extrusion, or separation under low pressure. In particular, such a coating can be applied to one or more optical fibers immediately after stretching by dipping, spraying, extrusion, or separation under low pressure. In particular, by applying the coating immediately after stretching the one or more fibers, it is possible to achieve a nearly perfect fire-polished surface for the one or more fibers before they come into contact with other materials or other fibers. This can at least mitigate micro-damage that reduces the strength of the one or more fibers. In principle, it is even conceivable that such a coating can also restore any previous damage or at least partially mitigate the effects of such damage. Protection against hydrolytic corrosion can also be achieved.

[0116] Such layers are usually applied in such a way that the freshly stretched optical waveguide is drawn as a fiber through a crucible having a nozzle in which the polymer material to be applied is located, wherein the layer thickness can also be adjusted by means of the nozzle.

[0117] The layer thickness of the coating is generally in the range from 5 μm to 100 μm, preferably in the range from 10 μm to 50 μm.

[0118] In addition, it can be provided that, in addition to the first coating, at least one further organic coating can be applied. This additional coating is also called a buffer layer and is usually applied to quartz fibers. As materials for this buffer layer, PMMA, polyamide, Polyimide or fluorinated polymer, such as ethylene tetrafluoroethylene copolymer (ETFE), which is available for example under the trade name This additional coating serves to increase the robustness of the flexural strength. In particular, the buffer layer may also contain a thermoplastic elastomer, such as a thermoplastic polyester elastomer or a thermoplastic copolyester elastomer, such as those available under the trade name Commercially available, and / or polyvinylidene fluoride (for example available under the trade name Kynar), or polytetrafluoroethylene (for example available under the trade name Teflon), or polyurethane. Such a buffer coating can be applied, for example, by spraying, dipping, extrusion and electrostatic methods.

[0119] Such a layer system can be produced, for example, from a two-layer system, in which a thinner layer, typically 10 μm to 50 μm thick, for example made of acrylate or epoxy compounds, is first applied to the light guide body and then a thinner layer, for example made of A so-called buffer layer made of PMMA or polyimide serves as further mechanical protection, which can also have a significantly thicker wall thickness, typically 50 μm to 200 μm.

[0120] For applications where space is at a premium, a first coat is sufficient to ensure the highest possible flexural strength.

[0121] It should be noted that other methods, particularly for increasing fiber strength, are also conceivable. For example, a targeted temperature process similar to the thermal tempering of glass can create a higher compressive toughening near the surface, which increases the fiber's flexural strength. Chemical hardening of the fiber is also conceivable. However, to achieve the fiber's optical properties, an additional cladding is required, in which targeted additional compressive toughening can be created by ion exchange in molten salt or by subsequent tempering and spraying of a salt layer. Electron or ion beam hardening is also conceivable. However, these latter methods are relatively complex. Furthermore, maintaining the fiber's optical properties is difficult.

[0122] According to another embodiment, the coating can also be designed to block light, ie, to be opaque or light-absorbing, for example colored, such as black or blue. This is advantageous because crosstalk on the camera chip can be reduced in this way.

[0123] In a particularly advantageous embodiment, the optical waveguide includes at least one glass fiber, in particular a glass fiber containing or composed of a multi-component silicate glass, or is preferably configured as a glass fiber bundle, in particular a glass fiber bundle comprising glass fibers containing or composed of a multi-component silicate glass, or consisting of glass fibers made of a multi-component silicate glass. This is because such glass fibers allow the optical properties of the glass fiber bundle containing these glass fibers to be adjusted in a particularly flexible manner, and thus the optical properties of the optical waveguide or endoscope. Furthermore, such optical waveguides based on glass fibers have a significantly higher temperature resistance than polymer optical fibers (POFs). This is particularly important for achieving particularly good coupling efficiency, for example, when a thin fiber bundle composed of or containing glass fibers is in direct contact with an LED chip or in close proximity to such a chip. However, polymer optical fibers or fiber bundles composed of or containing polymer optical fibers cannot withstand such thermal loads, otherwise the fibers would melt.

[0124] According to one embodiment, an optical fiber or a plurality of optical fibers are held at the proximal end of a coupling sleeve, which is designed as a mechanical interface to the laser light source and thus enables a defined light coupling in terms of the focusing distance and the centering relative to the light source. In the case of one or more single fibers, ideally three or seven single fibers, so-called SMA plugs can be provided as coupling sleeves, for example, which in particular enable a defined orientation of the laser light source and can also be used in particular for laser applications. For this purpose, so-called FC plugs are also conceivable. Here again, the arrangement of seven single fibers is particularly advantageous, since, on the one hand, a substantially circular cross-section can be achieved and, on the other hand, the wedge area between the individual fibers is relatively small. The smallest possible size. This has advantages in terms of coupling efficiency. The wedges are the gaps between the round fiber bundles. Another optimal fiber arrangement is achieved with 19 individual fibers, which are optimally packed tightly around a central fiber in two shells. These individual fibers are typically fixed using an adhesive, such as a two-component thermally crosslinked epoxy adhesive, or a UV-curing adhesive.

[0125] To improve coupling efficiency, the optical fibers can also be arranged at the proximal end by heat-melting. This process, due to the thermal deformation process, deforms the originally round individual fibers into an at least approximately hexagonal cross-section, minimizing the wedge area and enabling a nearly gap-free arrangement. Furthermore, given a predetermined coupling cross section or focusing diameter, more fibers can be positioned, thereby transmitting a higher light flux.

[0126] Such a hot melt fiber can be arranged, for example, at the proximal end, which is coupled into a sleeve. However, the hot melt fiber can also be presented without a sleeve at the proximal end. For embodiments requiring efficient use of space, it is particularly advantageous to have a particularly small area cross section, for example at the proximal end.

[0127] According to another embodiment, at least one optical fiber and / or multiple optical fibers and / or the optical conductor are deformed at the distal end compared to the proximal end. This means that, according to one embodiment, at least one optical fiber and / or multiple optical fibers and / or even the optical conductor itself can have a cross-sectional plane with a different shape at the distal end than at the proximal end. For example, the cross-sectional plane of a fiber and / or multiple fibers and / or the optical conductor can be essentially circular at the proximal end (within the measurement accuracy range), but exhibit an oval, kidney-shaped, or essentially D-shaped cross-section at the distal end. Different optical fibers can also have different cross-sectional planes; in particular, the cross-sectional plane at the proximal end can be circular, while one or more fibers have an oval shape at the distal end, while other fibers have a kidney shape. Other cross-sectional planes are also conceivable, such as a rectangular or approximately rectangular cross-sectional plane, especially at the distal end, or a generally polygonal cross-sectional plane. Furthermore, the cross-sectional shape of a fiber and / or multiple fibers and / or an optical fiber at the proximal and / or distal ends can be defined by at least two lines having different radii of curvature and / or can be configured as differential planes of two only partially overlapping circles and / or ellipses. In particular, the cross-sectional shape can be configured as a circular segment, wherein the radius of curvature is infinite, i.e., a straight line within the range of measurement accuracy. A cross-sectional plane configured as a circular segment in this manner can also be referred to as a D-shaped cross-sectional plane or a substantially D-shaped cross-sectional plane.

[0128] In particular, the approximately D-shaped cross section provides a high degree of utilization of the available cavity and can therefore increase the light flux or illumination intensity at the distal end of the endoscope. In the context of the present disclosure, a substantially D-shaped cross section or a substantially D-shaped cross-sectional plane refers in particular to a surface configured as a circular segment.

[0129] Such an embodiment can be particularly advantageous for ensuring a particularly advantageous spatial arrangement of the fiber and / or fibers and / or the optical waveguide relative to the camera chip.

[0130] Generally, at least within the measurement accuracy range, at least one optical fiber and / or a plurality of optical fibers can have a cross-sectional plane whose at least partial shape deviates from a circle. This can help to realize a particularly effective arrangement of each element in the second component of the endoscope, for example a space-saving arrangement.

[0131] This is particularly advantageous at the distal end of the light guide.

[0132] According to one embodiment, at least one optical fiber and / or multiple optical fibers have, at least at the distal end of the optical fiber, a cross-section with a flattened shape and an aspect ratio of at least 1.5:1, and / or an oval cross-section and / or a kidney-shaped cross-section, and / or a cross-section that is bounded by at least two lines with mutually different radii of curvature and / or is constructed as a differential plane of two only partially overlapping circles and / or ellipses.

[0133] According to another embodiment, the numerical aperture of the one or more optical fibers is at least 0.7, preferably at least 0.8, and particularly preferably at least 0.85. Preferably, the core of the one or more optical fibers comprises a glass material having a composition selected from the aforementioned glass composition and glass combination ranges for the core glass. In particular, the core of the glass fiber can consist primarily (i.e., at least 50% by weight), essentially (i.e., at least 90% by weight), or even completely of such a glass material.

[0134] An embodiment in which the core of one or more optical fibers comprises such a glass material is advantageous, since this enables an excellent field of view of the camera (here in particular for a 1×1 mm field of view, for example). 2 area is illuminated by the so-called C-MOS camera).

[0135] According to a further embodiment, the optical fiber or fibers are constructed such that the core and / or cladding glass of the optical fiber or fibers does not contain lead and / or other heavy metals, nor antimony and / or arsenic and / or other critical elements, such as Cr(VI) (hexavalent chromium), except for unavoidable traces.

[0136] Another aspect of the present invention relates to a disposable endoscope system comprising a first component and a second component separately packaged in a sterile manner, the second component preferably being constructed or configurable as a shaft which can be detachably coupled to the first component after being removed from its sterile packaging to obtain an endoscope, in particular an endoscope according to an embodiment of the present disclosure.

[0137] In the context of this disclosure, a shaft refers to a second component of an endoscope that has a very small cross-sectional area compared to its length. In other words, the shaft is very thin compared to its length. This embodiment of the second component as a shaft is particularly advantageous when inspecting difficult-to-access areas with endoscopy and / or in medical technology applications.

[0138] An advantage of the endoscope system according to the present disclosure is that the second component, in particular the shaft, is already sterilely packaged for rapid, sequential examinations, enabling rapid inspection of multiple areas or, in medical examinations, multiple examinations of different patients in rapid succession while ensuring adequate hygiene. Therefore, it is particularly advantageous for the endoscope system according to the present disclosure that the second component can be detachably coupled to the first component, thereby achieving the advantages of a disposable endoscope while, for example, not requiring sterilization of the various components of the endoscope system during medical examinations or other medical applications, being housed in the reusable first component. This makes it possible, for example, to illuminate even disposable endoscopes with laser light.

[0139] According to one embodiment, a second component is provided that is designed as an at least partially flexible shaft. The shaft includes a flexible sheathing comprising a hose, braided tube, or heat-shrink tubing, which at least partially surrounds the optical fiber with its at least one optical fiber, as well as a power supply line for feeding the camera chip and preferably at least one feedback signal line to a data and / or image processing unit, which can be a component of the first component. This embodiment, in particular with a flexible shaft, is particularly suitable for medical applications.

[0140] According to another embodiment, a second component is provided that is designed as an at least partially rigid shaft and includes a rigid sheath with a sleeve, which surrounds the optical conductor with its at least one optical fiber, as well as a power supply line for feeding the camera chip and at least one feedback signal line to a data and / or image processing unit, which can be a component of the first component. This embodiment is particularly advantageous because it allows for better protection of the components contained in the second component (here designed as a rigid shaft) from mechanical loads.

[0141] Another aspect of the present disclosure relates to a light source for an endoscope, in particular, a light source for an endoscope according to an embodiment of the present disclosure. The light source for an endoscope, in particular, an endoscope according to an embodiment of the present disclosure, comprises a laser for emitting primary light, preferably blue light and / or ultraviolet light, and at least one converter associated with the laser, and an optical fiber having one or more optical fibers, wherein the laser is arranged such that the laser light at least partially illuminates a surface of the converter, and the optical fiber receives the light converted and scattered or emitted by the converter at the proximal end of at least one optical fiber.

[0142] This light source embodiment can increase the coupling efficiency because, for example, an optical fiber or optical fibers with a high numerical aperture relative to air can be used. In this way, the excitation laser can also be spatially decoupled from other components of the endoscope, so that, for example, these components can also be protected from excessive heating by the laser.

[0143] In general, without being limited to the examples above, the light source can also include more components or members. In particular, the light source can include, for example, optical elements that can deflect and / or modify, in particular align, the laser light. For example, such a member can be embodied or designed as a diffractive optical element (DOE). In such an embodiment, it can be advantageous, for example, if the DOE is designed so that at least one surface of the converter is fully illuminated or so that the laser light is deflected onto a plurality of different converters or converter elements. However, it is also possible to provide optical elements that do not align and / or deflect and / or modify the primary light, but rather deflect and / or modify and / or align the secondary light (i.e., the converted and / or scattered light).

[0144] In particular, a diffuser arranged at the distal end can be provided, which emits the light guided by the fiber over a wider spatial angle and can thus illuminate a larger tissue area.

[0145] According to another embodiment, the light source includes an optical fiber for guiding the laser light to the converter. The outcoupling end of the optical fiber and the coupling end of the optical fiber are directed toward the same surface of the converter, so that the converter operates in diffuse reflection. The direction of light conduction in the optical fiber for guiding the laser light is opposite to the direction of light conduction coupled into the optical conductor by the converter. This prevents direct laser light from being coupled into the optical conductor of the endoscope, which is highly advantageous from a safety perspective. In particular, in the event of a converter failure, this arrangement prevents extremely intense laser light or the primary radiation of the laser light source from directly reaching the patient's tissue. It should generally be noted that the converter in this arrangement is thermally conductively connected to a heat sink (e.g., in the form of a cooling element) as a passive component or to an active cooling device. Furthermore, if the converter is damaged or even completely destroyed, it can also be configured as a so-called beam dump.

[0146] According to a further embodiment, the converter comprises two converter elements, wherein the converter elements each contain a ceramic converter material, wherein preferably the converter elements contain different converter materials, so that the converter elements convert the laser light into light with different spectral compositions, wherein at least one laser is provided which irradiates the two converter elements with a laser beam respectively.

[0147] Also conceivable is a single converter which consists of a mixture of two converter materials which emit light of different wavelengths.

[0148] This embodiment enables a particularly good CRI to be achieved, ie a particularly good color reproduction.

[0149] Preferably, the optical fiber has two coupling ends, wherein the converter element is arranged in such a way that the light emitted by the converter element is coupled into each of the coupling ends.

[0150] Generally, the light source can be designed such that it comprises a plurality of converter elements, wherein the optical waveguide is designed such that it has a plurality of coupling-in ends, wherein the converter elements are arranged such that the light emitted by the converter elements is respectively coupled into one of the coupling-in ends, wherein the number of converter elements corresponds to the number of coupling-in ends, so that each converter element is preferably associated with a respective coupling-in end.

[0151] With this embodiment, particularly high CRI values ​​can be achieved. The reason for this is that the optical fiber already has added color mixing.

[0152] It can be particularly advantageous if the luminous flux portion coupled into the optical waveguide is adjustable. This allows the color position of the light generated by the light source to be adjusted in a particularly simple manner. Therefore, according to one embodiment, the light source has a device for adjusting the luminous flux portion coupled into the optical waveguide by two converter elements or by all converter elements comprised by the light source. BRIEF DESCRIPTION OF THE DRAWINGS

[0153] The present invention will be described in detail below with reference to the accompanying drawings. The same reference numerals represent the same or corresponding elements.

[0154] Figure 1 shows a schematic diagram, not drawn to scale, of an endoscope according to one embodiment;

[0155] Figure 2 a schematic diagram, not drawn to scale, showing the distal end of an endoscope; and

[0156] Figure 3 and Figure 4 A schematic diagram, not drawn to scale, shows portions of a light source according to some embodiments. DETAILED DESCRIPTION

[0157] Figure 1 1 is a schematic diagram of an endoscope 1 according to an embodiment, not drawn to scale. The endoscope 1 comprises a first component 7 and a second component 5, wherein the first component is arranged on the left side in the figure and the second component 5 is located on the right side in the figure. The second component 5 comprises a proximal end 50 connected to the first component 7. It can be provided that the proximal end 50 of the second component 5 connected to the first component 7 is designed to be detachable. In particular, the two components 5 and 7 are designed so that they are designed with the aid of a detachable connection. This is particularly advantageous when one component is only used for single use and the other component (for example, the first component 7 in this case) contains components for multiple use, in particular those of high quality and / or high cost. In particular, this is the case when a special light source (for example, a light source comprising at least one laser) is contained in one of the components (for example, the first component 7 in this case).

[0158] The second component also has a distal end 51, in which a camera chip 15 for image acquisition is arranged. A light conductor 9 comprising at least one optical fiber 11 also extends within the second component 5. The optical fiber 11 is designed to guide light from the light source 3 from the proximal end 50 of the light conductor 9 to the distal end 51 of the light conductor 9 and emit it at the distal end 51. A power supply line (not shown) for supplying power to the camera chip 15 also extends within the second component 5.

[0159] Light source 3 includes at least one laser 10 designed to emit primary light and a converter 17 that at least partially converts the light from laser 10 into light of a different wavelength and emits the light. Converter 17 is coupled to proximal end 50 of second component 5 connected to first component 7, so that the light converted and emitted by converter 17 is coupled into optical fiber 9.

[0160] The converter 17 preferably comprises a ceramic converter material.

[0161] The converter 17 can be designed in this respect such that it comprises at least two ceramic converter materials which convert the light of the laser 10 (or the laser light) into light having different spectral compositions.

[0162] Generally, not limited to Figure 1 The endoscope 1 shown in the example or according to Figure 1 In the exemplary endoscope 1 of FIG. 1 , the light source 3 including the laser 10 is comprised. The converter 17 can be understood as a converter element (not shown in the figure) comprising a converter material. In particular, the converter element can be designed such that it comprises a converter material, and for example, it is particularly preferred that the converter material can be or comprise a ceramic material, which is applied, for example, in the form of a thin material layer to a substrate that can serve as a conductor for the thermal energy generated when converting the primary light. This embodiment is particularly preferred when the light source or converter operates in diffuse reflection.

[0163] According to one embodiment of the endoscope, the converter 17 is optically coupled to the optical waveguide 9, so that the light diffusely reflected by the converter 17 is coupled into and / or can at least be coupled into the optical waveguide 9. Preferably, the laser 10 can be arranged and directed toward the converter 17 so that only the light converted and / or scattered by the converter 17 is coupled into and / or can at least be coupled into the optical waveguide 9. From a safety perspective, this design is particularly ideal to prevent high-energy laser light from reaching, for example, the tissue surface 80 (here, for example Figure 1 (shown on the left in ).

[0164] Advantageously, provision can be made for the laser 10 to be arranged such that the light from the laser 10 is directed onto the converter 17 and / or can be deflected thereto counter to the light emission direction of the light converted by the converter 17 and coupled into the optical waveguide 9 .

[0165] Particularly from an assembly perspective, especially when the second component 5 is intended for single use only, it can be advantageous if the light guide 9 has a maximum of ten optical fibers 11. Generally, however, up to several hundred individual fibers 11 can be present in the light guide 9, depending on the respective fiber diameter and the thickness of the resulting or obtained fiber bundle, and thus on the thickness of the light guide 9, and the number of fibers 11 can be selected accordingly.

[0166] Typical fiber diameters (or fiber thicknesses) of the optical fibers 11 can preferably be in the range of 100 μm to 1000 μm, preferably up to 600 μm, with the maximum fiber diameter particularly preferably being in the range of 150 μm to 400 μm. However, thin fibers with diameters of 30 μm, 50 μm or 70 μm are also conceivable.

[0167] According to one embodiment, the optical fiber 11 or the optical fibers 11 are designed as step-index glass fibers.

[0168] Preferably, the optical fiber 11 and / or the optical fibers 11 can be configured such that the numerical aperture (NA) of at least one fiber 11 and / or the optical fibers 11 relative to air is at least 0.7, preferably at least 0.8, and particularly preferably at least 0.85. This is particularly advantageous for achieving a high CRI (Color Rendering Index).

[0169] In particular from an assembly point of view, it may be advantageous if at least one optical fiber 11 or a plurality of optical fibers 11 are also provided. Figure 1 The optical fiber 9 is schematically shown to be arranged at its proximal end 50 in a coupling-in sleeve 55 .

[0170] The second member 5 can be configured as an at least partially flexible shaft, or can also be configured as an at least partially rigid shaft. The second member can, for example, include a sheath 53 (e.g. Figure 1 (illustrated as an example). If the component 5 is designed as an at least partially flexible shaft, the sheath 53 is of flexible design, in particular, using a hose or braided tube or heat shrink tubing. If the second component 5 is designed as an at least partially rigid shaft, the sheath 53 is preferably rigid and comprises a sleeve. Generally, and not limited to the example illustrated in this figure, the sheath 53 at least partially surrounds the optical fiber 9 having at least one fiber 11, the power supply line for feeding the camera chip 15, and preferably at least one feedback signal line 12, preferably a signal line to a data and / or image processing unit 18, which can in particular be a component in the first component 7.

[0171] As a particularly preferred embodiment, seven optical fibers 11 with a thickness of approximately 200 μm, which are designed as so-called wide-angle fibers with an NA>0.85, are arranged, wherein these seven optical fibers 11 are arranged around the camera chip 15 and are glued at their proximal ends into a common coupling sleeve 55. Alternatively, these seven optical fibers 11 can also be heat-fused into the coupling sleeve 55. However, it is generally possible and even preferred to have heat-fused fibers without a sleeve at the proximal end.

[0172] Figure 2 A schematic diagram showing the distal end 51 of the second member 5 of the endoscope 1 is shown, but in Figure 2 The distal ends 51 each contain an optical fiber 9 , which in each case contains a plurality of fibers 11 , and a camera chip 15 .

[0173] Figure 2 In a.), four fibers 11 are arranged, which have a circular cross section within the measurement accuracy range. They are arranged around a camera chip 15, which has an approximately square shape, for example, so that there is a fiber 11 on each side of the camera chip 15. In contrast, in Figure 2 In d.), the fibers 11 are arranged only on three sides of the camera chip 15 .

[0174] exist Figure 2 In b.), two optical fibers 11 are arranged only on two sides of the camera chip 15. Here, the cross-section of the optical fibers 11 is not circular, but rather oval or elliptical. In particular, the optical fibers 11 can be configured so that they are deformed at the distal end 51 (as opposed to the proximal end 50, not shown), as shown here. In particular, the optical fibers 11 can have a circular cross-section at the proximal end 50 and be deformed at the distal end, as shown here. This can facilitate the arrangement of the fibers 11 around the camera chip.

[0175] Preferably, as shown here by way of example, the plurality of optical fibers 11 and / or at least one optical fiber 11 can have a flattened cross section, at least at the distal end 51, in particular with an aspect ratio of at least 1.5:1 and / or an oval and / or kidney-shaped cross section. Other cross-sectional shapes are conceivable, such as a polygonal shape, but a precisely flattened shape is particularly advantageous for arranging the optical fibers 11 around the camera chip 15. Figure 2 c.) shows an arrangement in which four fibers are arranged around the camera chip 15 and have a substantially D-shaped cross section at the distal end.

[0176] Not only Figure 2 b.) and in Figure 2The distal end of the fiber 11 shown in c.) can be deformed, for example, by a thermoforming process in the manner shown so as to be configured in Figure 2 The corresponding cross-sectional planes or cross sections shown in a.) to d.) of FIG. For this purpose, the fiber 11 is heated in a mold above its processing temperature and then deformed under pressure. Of course, due to the viscosity of the fiber material, a perfect geometry cannot be reproduced. Therefore, the essentially D-shaped cross-section has a small radius at the tapering corners. In principle, this shaping can be applied to glass fibers, quartz fibers or plastic fibers, the shaping temperature being adapted to the respective material. The temperatures used for plastic fibers (POFs) are typically 150°C to 300°C, for glass fibers 500°C to 800°C, and for quartz fibers up to 2000°C.

[0177] As mentioned above, Figure 2 e.) shows an arrangement of 12 fibers. Here, a total of four coarse fibers 11 are grouped with eight thin fibers, so that in each cavity (segment), the coarse fiber 11 is placed in the center of the cavity, and two thin fibers 11 are placed to the left and right of the coarse fiber 11. This way, despite the relatively small number of fibers 11, the cavity area is well utilized, thus achieving a relatively high light flux. This type of example can also be expanded to an arrangement with 20 individual fibers 11, i.e., five fibers 11 per cavity, ideally with three diameter grades.

[0178] at last, Figure 3 and Figure 4 Two schematic diagrams showing parts or sections of the light source 3 are not drawn to scale.

[0179] The light source 3 for an endoscope 1, in particular for an endoscope according to the present disclosure, includes a laser 10 (not shown) for emitting primary light, preferably blue and / or ultraviolet light, as well as at least one converter 17 and an optical fiber 90 associated with the laser. The converter 17 is designed to include a first converter element 170 containing a ceramic converter material 173. The converter element 170 is designed such that the ceramic converter material 173 is present as a material layer on a substrate or heat sink 172, also contained within the converter element. The substrate or heat sink can be configured, for example, to conduct heat energy generated by the conversion of the laser light. Furthermore, the optical fiber 90 is provided, including one or more optical fibers 11. The laser 10 (not shown) is arranged such that the light from the laser 10 at least partially illuminates a surface of the converter 17, in particular a surface 175 formed at least partially by the converter material 173, and the optical fiber receives the light converted and / or scattered and / or emitted by the converter 17 at the proximal end of at least one optical fiber 11.

[0180] According to Figure 3 In the illustration in FIG, it can be provided that the optical fiber 100 feeds the laser light to the converter 17. In this case, as Figure 3 As shown by way of example in FIG, the outcoupling end of the optical fiber 100 and the coupling-in end 91 of the optical waveguide 90 are preferably oriented toward the same surface 175 of the converter 17, so that the converter operates in diffuse reflection. In this case, the direction of light conduction in the optical fiber 100 is opposite to the direction of light conduction coupled into the optical waveguide 90 by the converter. Advantageously, provision can be made for the optical waveguide 90 to have a connection to the optical waveguide 9 of the second component 5 of the endoscope at its distal end 93. The light source 3 may also have optical elements (shown here in the form of lenses 96), in particular so-called diffractive optical elements, for example, for beam shaping, focusing, and / or collimation.

[0181] Figure 4 A section or portion of a light source 3 including a laser 10 (not shown in this figure) is shown. The converter 17 comprises two converter elements 170 and 171. Converter element 170 comprises a first converter material 173, in particular a ceramic converter material 173, and converter element 171 comprises a second converter material 174, in particular a ceramic converter material 174. Converter materials 173 and 174 are designed to be different, so that converter elements 170 and 171 convert laser light into light with different spectral compositions. For example, converter material 173 can be configured as a so-called "red phosphor," while converter material 174 can be configured as a so-called "yellow phosphor." This embodiment is particularly advantageous for optimizing the so-called CRI, in particular achieving a CRI above 80.

[0182] Generally, the light source 3 can include a plurality of converter elements 170 , 171 , in which case the number of coupling ends 91 , 92 of the optical waveguide 90 preferably corresponds to the number of converter elements.

[0183] In particular, at least one optical fiber 100 is provided, which directs the light of the laser 10 toward the surface 175 of the converter elements 170 , 171 . The number of optical fibers 100 also preferably corresponds to the number of converter elements 170 , 171 , as the figure shows two converter elements by way of example. The figure also shows the distal end 93 of the optical fiber 90 , where the connection to the optical fiber 9 of the second component 5 can preferably be provided.

[0184] Reference Signs List

[0185] 1 Endoscope

[0186] 3 Light Source

[0187] 5. Second component of the endoscope (e.g., shaft)

[0188] 50 Proximal end of the second member

[0189] 51 distal end of the second member

[0190] 53 sheath

[0191] 55 coupling sleeve

[0192] 7. The first component of the endoscope

[0193] 9, 90 photoconductor

[0194] 91, 92: coupling end of optical fiber 90

[0195] 93 distal end (interface) of optical conductor 90

[0196] 96 Optical elements (e.g. lenses)

[0197] 10 Laser

[0198] 11.100 optical fiber

[0199] 12 Feedback signal line

[0200] 15 Camera Chip

[0201] 17 Converter

[0202] 170, 171 converter components

[0203] 172 Heat Sink

[0204] 173, 174 Converter Materials

[0205] 175 Surface of the converter

[0206] 18 Data and / or image processing unit

Claims

1. An endoscope (1), comprising a first component (7) and a second component (5), wherein a light source (3) is built into the first component (7), and wherein the second component (5) has a proximal end (50) detachably connected to the first component (7) and has a distal end (51), wherein a camera chip (15) or an optical fiber element for image acquisition is arranged in the distal end (51), and wherein an optical conductor (9) having at least one optical fiber (11) extends in the second component (5) to guide light from the light source (3) from the proximal end (50) to the distal end (51) and emit it at the distal end (51), and a power supply for feeding the camera chip (15) extends. The light source (3) comprises at least one laser (10) for emitting primary light, and a converter (17) for converting the light of the laser (10) at least partially into light of a different wavelength and emitting the light, wherein the converter (17) is coupled to a proximal end (50) of the second component (5) connected to the first component (7) so that the light converted and emitted by the converter (17) is coupled into the optical conductor (9), wherein the at least one optical fiber (11) is a step-index glass fiber, wherein the glass composition of the at least one optical fiber (11) does not contain lead and / or other heavy metals, nor does it contain antimony and / or arsenic and / or other important elements except for unavoidable traces.

2. The endoscope (1) according to claim 1, wherein the glass composition of the at least one optical fiber (11) is free of Cr(VI) except for unavoidable traces.

3. The endoscope (1) according to claim 1 or 2, wherein the converter (17) comprises a ceramic converter material (173, 174). 4 . The endoscope ( 1 ) according to claim 3 , wherein the converter ( 17 ) comprises at least two ceramic converter materials ( 173 , 174 ) which convert the laser light into light having different spectral compositions.

5. The endoscope (1) according to claim 4, wherein the converter (17) comprises two converter elements (170, 171), wherein the converter elements (170, 171) each contain one of the ceramic converter materials (173, 174), so that the converter elements (170, 171) convert the laser light into light of different spectral compositions.

6. An endoscope (1) according to claim 1 or 2, wherein the converter (17) is optically coupled to the optical waveguide (9) so that light diffusely reflected by the converter (17), i.e. light converted and / or scattered and / or reflected, is coupled and / or can at least be coupled into the optical waveguide (9).

7. The endoscope (1) according to claim 1 or 2, wherein the laser (10) is arranged and oriented facing the converter (17) in such a way that only light converted and / or scattered and / or reflected by the converter (17) is coupled and / or can at least be coupled into the optical waveguide (9).

8. The endoscope (1) according to claim 1 or 2, wherein the laser (10) is arranged such that the light of the laser (10) is directed onto the converter (17) and / or can be deflected thereto substantially counter to the light emission direction of the light converted by the converter (17) and coupled into the optical waveguide (9).

9. The endoscope (1) according to claim 1 or 2, wherein the optical fiber (9) has at most twenty optical fibers (11), wherein the individual optical fibers (11) can have different diameters. 10 . The endoscope ( 1 ) according to claim 9 , wherein the optical fiber ( 9 ) has at most ten optical fibers ( 11 ).

11. The endoscope (1) according to claim 9, wherein the diameter of the optical fiber or fibers (11) is in the range of 100 µm to 1000 µm.

12. The endoscope (1) according to claim 9, wherein the diameter of the one or more optical fibers (11) is in the range of 100 µm to 600 µm.

13. The endoscope (1) according to claim 9, wherein the diameter of the one or more optical fibers (11) is in the range of 150 µm to 400 µm.

14. Endoscope (1) according to claim 1 or 2, wherein the one or more optical fibers (11) have a numerical aperture (NA) of at least 0.7 relative to air.

15. Endoscope (1) according to claim 14, wherein the numerical aperture (NA) is at least 0.

8.

16. The endoscope (1) according to claim 14, wherein the numerical aperture (NA) is at least 0.

85.

17. Endoscope (1) according to claim 1 or 2, wherein the one or more optical fibers (11) have a polymer-based coating on their side surfaces or a sheath made of a polymer-based hose material.

18. The endoscope (1) according to claim 17, wherein The coating is made of an acrylate-based, polyamide-based, polyurethane-based, polyimide-based, epoxy-based, ethylene-tetrafluoroethylene copolymer-based or polyxylene-based compound or a mixture of these compounds. and / or, wherein the coating can be applied or applied to one or more optical fibers (11) directly under low pressure by means of dipping, spraying, extrusion or deposition after the fibers (11) have been stretched, and / or, The coating has a layer thickness of 10 μm to 100 μm.

19. The endoscope (1) according to claim 17, wherein the layer thickness of the coating is 20 µm to 50 µm.

20. The endoscope according to claim 17, wherein the coating has at least one additional outer coating, which can be made of PMMA, polyamide, polyimide or fluorinated polymer or a mixture thereof.

21. The endoscope of claim 20, wherein the fluorinated polymer is ethylene tetrafluoroethylene.

22. The endoscope (1) according to claim 1 or 2, wherein one or more optical fibers (11) are arranged in a coupling-in sleeve (55) at the proximal end (50).

23. The endoscope (1) according to claim 1 or 2, wherein the optical fiber (11) is arranged at the proximal end (50) in a hot-melt manner.

24. Endoscope according to claim 1 or 2, wherein one or more optical fibers (11) and / or the optical conductor (9) are deformed at the distal end (51) relative to the proximal end (50).

25. Endoscope according to claim 1 or 2, wherein one or more optical fibers (11) have a flattened cross-section at least at the distal end (51) of the optical fiber (9) with an aspect ratio of at least 1.5:1, and / or wherein the shape of the cross-sectional plane is matched to the remaining area between the camera chip and the outer contour of the distal end.

26. The endoscope according to claim 25, wherein the shape of the cross-sectional plane is an oval cross section and / or a kidney-shaped cross section and / or a circular segment-shaped cross section.

27. A disposable endoscope system comprising a first component (7) and a second component (5) packaged separately in a sterile manner, wherein the second component (5) is constructed as a shaft rod, which can be detachably coupled to the first component (7) after being removed from its sterile packaging (20) to obtain an endoscope according to any one of claims 1 to 26.

28. A disposable endoscope system according to claim 27, wherein a second component (5) is provided which is constructed as an at least partially flexible shaft, the shaft comprising a flexible sheath (53) having a hose or a heat shrink tube, the sheath (53) at least partially surrounding the optical conductor (9) having at least one optical fiber (11) and a power supply line for feeding the camera chip (15) and at least one feedback signal line (12) to a data and / or image processing unit (18), the data and / or image processing unit (18) being a component in the first component (7).

29. The disposable endoscope system according to claim 28, wherein the flexible tube is a braided tube.

30. A disposable endoscope system according to claim 27 or 28, wherein a second component (5) is provided which is constructed as an at least partially rigid shaft, the shaft comprising a rigid sheath (53) with a sleeve, the sheath (53) surrounding the optical conductor (9) having at least one optical fiber (11) and a power supply line for feeding the camera chip (15) and at least one feedback signal line (12) to a data and / or image processing unit (18), the signal and / or image processing unit (18) being a component in the first component (7).

31. A light source (3) for an endoscope (1) according to any one of claims 1 to 26, the light source comprising a laser (10) for emitting primary light, at least one converter (17) associated with the laser, and an optical fiber (90) having one or more optical fibers (11), wherein the laser (10) is arranged such that the light of the laser (10) at least partially illuminates a surface (175) of the converter (17), and the optical fiber (90) of the light source receives the light converted and / or scattered and / or reflected by the converter (17) at the proximal end of its at least one optical fiber (11).

32. The light source (3) according to claim 31, wherein the laser (10) is configured to emit blue light and / or ultraviolet light.

33. The light source (3) according to claim 31 or 32 comprises an optical fiber (100) for guiding the laser light to the converter (17), wherein the coupling-out end of the optical fiber (100) for guiding the laser light to the converter and the coupling-in end of the optical conductor (90) of the light source are directed toward the same surface (175) of the converter (17), so that the converter (17) operates in diffuse reflection and the light conduction direction for guiding the laser light in the optical fiber (100) for guiding the laser light to the converter is opposite to the light conduction direction coupled from the converter (17) into the optical conductor (90) of the light source.

34. The light source (3) according to claim 31 or 32, wherein the converter (17) comprises two converter elements (170, 171), wherein the converter elements (170, 171) each contain a ceramic converter material (173, 174).

35. The light source (3) according to claim 34, wherein the converter elements (170, 171) contain different converter materials (173, 174), so that the converter elements (170, 171) convert laser light into light with different spectral compositions, wherein at least one laser (10) is provided which irradiates each of the two converter elements with a laser beam.

36. The light source (3) according to claim 34, wherein the optical waveguide (90) of the light source has two coupling ends (91, 92), wherein the converter elements (170, 171) are arranged such that the light emitted by the converter elements (170, 171) is coupled into each of the coupling ends (91, 92).

37. The light source (3) as claimed in claim 31 or 32, comprising means for adjusting the ratio of the luminous fluxes coupled into the optical waveguide by the two converter elements (170, 171).

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