DE102006062938B3 - Endoscopic system, has fluorescence converter designed as fluorescent body that is mounted downstream of light emergence surface of transmission path as separate interchangeable part, and distal end and body, which are inserted into fixture - Google Patents

Abstract

The system (1) has an excitation radiation source (5) arranged in a proximal supply unit (4), an optical radiation transmission path i.e. glass fiber (8), in an insertion piece (3), and a fluorescence converter at a distal end of the path. A laser diode (6) emits in a shortwave visible spectral range, which is used as the excitation radiation source. The fluorescence converter is designed as a fluorescent body that is mounted downstream of a light emergence surface of the path as a separate, interchangeable part. The distal end and the body are inserted into a lighting fixture (10).

Description

The invention relates to an endoscopic system having the features of the preamble of claim 1.

Out JP 2002-148 442 A An illumination device is known in which the light of a semiconductor laser is radiated into an optical glass fiber. The glass fiber consists of a high refractive index photoconductive core, a low refractive index cladding and a protective layer. Fluorescent dyes are embedded in the protective layer. The semiconductor laser emits in the spectral range 380-460 nm.

By discontinuities and impurities in the core and / or in the core / cladding boundary layer, part of the light is coupled out into the protective layer. The impurities can be introduced from the outside at a defined location. The decoupling can also be achieved by bending the glass fiber. The fluorescent dyes in the protective layer convert blue light of the semiconductor laser into yellow light μm. Another part of the decoupled blue light penetrates the protective layer and adds up with the yellow component to white light. The white light is emitted over the entire length of the glass fiber, which is provided with the protective layer and at which Auskoppelstörstellen are present. The device is intended essentially for lighting in display panels or for the representation of ornaments.

A further development of the principle of white light generation by additive color mixing of blue laser light and yellow light components generated in a fluorescence converter is lacking JP 2005-205 195 A known. The light emitted by an LED or a laser diode (LD) in the blue spectral region is fed by a condenser arrangement into a thin multimode glass fiber. The other end of the glass fiber is provided with a wavelength conversion element. This consists of the core of the glass fiber and a fluorescent material surrounding the tip of the glass fiber. Because of the white light generation concentrated at the tip of the optical fiber, the embodiment is particularly suitable for endoscopic applications. By selecting the laser emission wavelengths and the composition of the fluorescent material, a variety of color gradations in fluorescence conversion and color mixing is possible.

An optical device with white light generation at the distal end of the glass fiber was manufactured by the company Nichia Corp. Presented at the fair "Laser 2005" in Munich. A blue laser diode feeds shortwave bluish light with 405 or 445 nm wavelength into a thin multimode fiber. At the end of which is a fluorescence converter, which transmits part of the blue light and diffuses it. The other part of the bluish light is converted by the fluorescent dye into yellowish light and also diffused. Together with the directly transmitted blue light component, a white light is created by additive light mixing. Special emphasis was placed on an exact matching of the dyes and the scattering, so that the light acts as neutral as possible.

Due to the fiber end coating comprising the fluorescence converter, the light emission takes place in an angular range of virtually 360 °. The glass fiber can be introduced with the coated head part for illumination in cavities, as long as the resulting in the fluorescence conversion heat can be radiated without damage into the cavity.

Out JP 2005-328 921 A an adapter for endoscopes is known in which a fluorescent body is inserted. The adapter can be placed on the distal end of the endoscope so that the fluorescent body of the exit surface of an illumination fiber is opposite. By suitable shaping of the fluorescent body and coating of its outer surface can be achieved that the excitation light can enter the fluorescent body and the fluorescent light is reflected in the direction of the front surface of the fluorescent body. The front surface can be provided with a transparent protective layer.

From the publication EP 1 795 798 A1 For example, there is known a light-emitting device including an excitation light source, a light guide for transmitting the excitation light, and a wavelength-converting element at the distal end of the light guide. The light exit end of the light guide is arranged a scattering body for expanding the excitation beam before entering the wavelength converting element.

Out US 2006/0235277 A1 an insertion part for an endoscope is known in which a phosphor is arranged at the distal end in front of the light guide. The radiation emitted by the phosphor is radiated out of the insertion part by an illumination lens.

Out JP 2006-158789 A is a distal end of an endoscope known in which centrally a CCD camera camera is used for observation. Around the camera, three light guides are arranged, which illuminate the field of observation. At the light exit surfaces of the light guide fluorescent substances for red, green and blue emission are arranged. In addition, the Light exit surfaces of the optical fiber be preceded by optical means with which the illumination cone are deflected towards the center. The deflection means can also be arranged in a cap which is placed on the distal end.

From the publication DE 20 2004 012 992 U1 is an endoscopic video measuring system with an introduction part and an attachable replaceable head known. In the introduction part, a single-mode optical fiber is arranged for transmitting a measuring radiation, which is assigned to the distal end part of an optical system for generating a collimated measuring beam.

Newer laser light sources are offered with ever-increasing power output. This leads to an increase in the thermal load of the fluorescence converter, whereby its life is reduced. The thermal stability of the fluorescence converter can be increased by the transition from organic to inorganic fluorescent components. However, this leads to an even higher heat radiation at higher light emission.

The concept of this white light generation by mixing a remainder of the blue excitation light with the fluorescent light is similar to that of the well-known white light LEDs. The fluorescent dyes are applied to these LEDs directly on the blue glowing LED chip. Unfortunately, these white light LEDs have the great disadvantage that they currently have about only 1 to 3 times the efficiency of electrical energy (watts) to emitted light (lumens) such as halogen lamps. Therefore, they also develop a lot of waste heat, which makes them unsuitable for endoscopic applications at the distal end. Since the heat dissipation at the distal end is usually poor, there may be generated by the lighting, no great heat, as this represents a risk of injury. This is especially important in video endoscopes, since their distal temperature-sensitive cameras themselves already generate a certain amount of waste heat.

The invention was based on the object of making use of the principle of the known white light generation in endoscopic systems for illumination and measuring beams with substantially forward or targeted sideways directed light emission and a heat load of the fluorescence converter, the examination subject and / or in the vicinity of the distal-side illumination optics to avoid attached endoscopic observation systems.

This object is achieved according to the invention in an endoscopic system of the type mentioned by the characterizing features of claim 1. Advantageous developments emerge from the features of the subclaims.

The arrangement of a detached from the glass fiber, separate and thus exchangeable fluorescent body opens up many possibilities of geometrical shaping to adapt to the specific requirements of an endoscope. But the optical properties of the fluorescent body can be varied varied by material selection and material composition. In addition, the interchangeability and installation of system units is much easier.

In addition to the light source for white light emission, miniaturization of light reflectors and beam shaping optics is of particular importance in endoscopy. If efficient beam shaping is required, the fluorescence body must be as small as possible with respect to the reflector or the beam shaping optics for reasons of optical geometry. However, this miniaturization inevitably increases the heat concentration and the destructive temperature gradient. For these reasons, the reduction of thermal resistances in and around the fluorescent body is important. In the subclaims concepts are mentioned, as can be achieved in miniaturized fluorescent bodies.

The term "fluorescent body" should also include its property as a scattering body for scattering the transmitted excitation light. The scattering is brought about by the scattering centers embedded in the volume of the fluorescent body and by structural effects on the surface. The scattering centers can also be the fluorophores at the same time. Due to their dimensioning, the scattering centers can selectively scatter the short wavelengths preferentially.

Embodiments of the system according to the invention are shown schematically in the drawing and are described in detail with reference to FIGS. Showing:

1 an endoscopic system with lighting fixtures,

2 a lighting fixture with glass fiber and fluorescent body,

3 the lighting fixture additionally with crystal window,

4 a replaceable head with a quasi punctiform fluorescence body,

5 the replaceable head 4 with focused excitation beam and

6 the replaceable head 4 with collimated excitation beam.

7a a larger fluorescent body in a replaceable head with sideways illumination and observation,

7b same arrangement with forward lighting and observation,

8th the replaceable head 7a additionally with parallel measuring beams,

9a the replaceable head 7a additionally with measurement pattern generation and

9b same arrangement in addition with video camera and electrical contacts.

1 shows schematically an endoscopic system 1 with eyepiece 2 and introductory part 3 , The introductory part 3 can be designed as a rigid tube or flexible. After or instead of the eyepiece with optical transmission of the observed image, a video camera with representation of the observed image can also be provided on a monitor. In a supply unit 4 is an excitation radiation source 5 arranged, which is a laser diode 6 and a coupling optics 7 for feeding the excitation light into a glass fiber 8th contains. Of course, it is also possible to provide additional laser diodes with emission of additional wavelengths, whose radiation also in the glass fiber 8th or in additional glass fibers can be fed. This can z. B. spectral weaknesses of the white light can be compensated. The laser diodes may be battery operated or powered by a power supply.

To connect the supply unit 4 with the endoscopic system 1 is a fiber optic cable 9 provided by special or commercially available connectors on the endoscope and the supply unit 4 is connected. The connectors can be designed in particular autoclavable and laser-protected. Through the introductory part 3 through is the glass fiber 8th in the usual way loose or in a separate illumination channel or in a protective cover led to the distal end. At the distal end is a lighting fixture 10 arranged in which the conversion into white light and the beam shaping to illuminate the object space or for the projection of elner measuring radiation done. The lighting fixture 10 is functionally replaceable and in a replaceable replaceable head at the distal end of the insertion part 3 integrated. The imaging optics is not shown here.

2 shows a variant of the lighting fixture 10 in detail. In a version 11 are the glass fiber 8th and a fluorescent body 12 used. The version 11 is z. B. made of a metal such as silver, copper or aluminum, and derives the heat from good in the fluorescent body 12 arises. The cross-section of the unprocessed cladding, sheath and core 8th is about 80-900 microns and about 5-900 microns on demand thinned, in the version 11 introduced distal end 8a , The thinning improves the heat dissipation to the proximal. The glass fiber can also with its full cross section in the socket 11 be used. The light exit opening 13 the version 11 widens funnel-shaped, z. B. conical from proximal to distal. In the cone-shaped part of the light exit opening 13 is a beam-shaping optical element 14 used.

In the construction of the lighting fixture 10 different parameters have to be considered. Generally, it is known in the illumination optical system that the ratio of the optical diameter (reflector, lens, lens) to the source diameter (incandescent filament, arc, LED chip, fiber end) is crucial for the possibility of beam shaping. With a point light source in relation to the optics, almost any intensity distribution can be generated. The light exit surface of the distal end of the fiberglass 8th is almost punctiform in this sense. However, the source of white light is through the fluorescent body 12 educated. Its smallest possible size depends in principle on at least four properties of the fluorescent material, namely the temperature resistance, the thermal conductivity, the light resistance and the optical density. All four of these material properties should be as high as possible. To the construction of the fluorescent body 12 To be able to perform punctiform as possible, must be given an efficient heat dissipation. Optimally, therefore, becomes a vitreous or transparent ceramic fluorescent body 12 chosen, which consists of reasons of temperature resistance only of inorganic parts. The inorganic, in the fluorescent body 12 bound fluorophores must be light-fast, so that they can also convert high incident light intensities without damage. The fluorophores and their concentration should be chosen so that no or only a small saturation by quenching occurs. To improve the heat dissipation to the proximal, the glass fiber diameter is to be limited by machining to the optically necessary minimum, which is represented by the thinning.

The light color and the light distribution arise in the illustrated construction directly in and near the fluorescent body 12 but overall in the lighting fixture 10 , This allows a modularity in the construction of the endoscopic Systems 1 , by matching the lens during fitting also the appropriate lighting fixture 10 consisting of fluorescent bodies 12 with socket 11 and beam shaping optics 14 can be chosen.

In the embodiment of the lighting fixture 10 to 3 is the fluorescent body 12 between two transparent panes 15 from a good heat-conducting material, eg. As a crystal or a transparent ceramic enclosed. Preferably, sapphire or diamond is chosen, with which the Fluroreszenzkörper 12 all around can dissipate its heat efficiently. It is particularly advantageous for heat dissipation, although the fluorescent body 12 is formed from transparent ceramics, doped sapphire or diamond doped with fluorescence centers, since then the heat source and the heat conductor largely coincide. It can also on one or both of the heat dissipating discs 15 be waived. The heat dissipating discs 15 In addition, they can also have optically imaging, scattering, reflective or diffractive properties.

The version 11 of the lighting fixture 10 can with advantage also from a special aluminum alloy, eg. As pure aluminum, be made so that it is possible in a simple manner, the surface of the cone-shaped light exit opening 13 to make highly reflective. If the version 11 z. B. consists of copper, the cone-shaped light exit opening 13 also silvered or coated with aluminum. The if necessary in the light exit opening 13 inserted optics 14 (Lens array, prism array, diffuser, diffractive optical element, aspherical lens, etc.) forms the illumination beam z. B. round or square and adjusts the beam angle to a not shown here observation lens. Essential to this is the hollow cone angle of the socket 11 , Important is the hollow cone, especially in the immediate vicinity of the fluorescent body 12 , From a distance of about 2-10x the diameter of the fluorescent body 12 can be dispensed with the conical shape and the resulting reflection direction. In addition to the illustrated cone, other curved shapes, such as parabola, ellipse, hyperbola, etc., are possible. Such forms should generally be referred to as funnel-shaped.

The fluorescent body 12 is in the 2 and 3 shown as a component with trapezoidal or rectangular longitudinal section and in a correspondingly shaped recess in the cone-shaped part of the light exit opening 13 the version 11 used. For attachment, the lateral surface of the fluorescent body 12 with a solderable, metallic coating, eg. As nickel, gold, titanium, silver, be provided. This allows a solid solder joint with good heat transfer to the socket 11 , In the case of non-solderable aluminum as a frame material can also be glued. Of course, the attachment of the fluorescent body 12 also be done by clamping, whereby an exchange is facilitated.

Because that's inside the fluorescent body 12 generated fluorescent light is emitted in all directions, it is advantageous, the lateral surface of the cone shape of the light exit opening 13 adjust and mirror before insertion. This supports forward emission from the fluorescent body 12 out and avoids light loss through backward scattering.

To adjust the color spectrum of the lighting fixture 10 can the Fluorenszenzkörper 12 also be constructed of several cascade layers containing different fluorescent dyes. By varying the respective layer thickness, the color spectrum can be influenced. The layer thickness can advantageously be modularly assembled in a simple manner by a number of thinner slices. This allows a quick and easy adjustment of the color spectrum to a standard in the assembly. This is especially helpful when producing the fluorescent body 12 or the fluorescent discs is not reproducible and subject to fluctuations in the spectrum.

The concept of the quasi-point light source according to the invention with a at the distal end of the insertion tube 3 coupled replaceable head 16 realized.

4 shows an embodiment in which a small, quasi point-like fluorescent body 12 on a good heat-conducting window 15 , z. B. a transparent ceramic, sapphire or diamond disc is arranged. The replaceable head 16 is in the direction of the arrow on the distal end of the insertion part 3 pushed, so that the light exit surface of the glass fiber 8th directly to the fluorescent body 12 is opposite. This arrangement requires high positioning accuracy. The construction elements windows 15 , Fluorescent body 12 and optics 14 can also be in a lighting fixture 10 summarized the type already described and as a unit in the replaceable head 16 be used.

The optics 14 are a deflection prism 17 and a lighting lens 18 downstream, with which a 90 ° deflected illumination beam cone 19 is produced. Shown in dashed lines are conventional components for video recording of the illuminated object.

At the in 5 illustrated embodiment is at the distal end of the insertion part 3 the light exit surface of the glass fiber 8th an imaging lens 20 upstream, the emerging excitation beam in deferred interchangeable head in the fluorescent body 12 focused. The fluorescent body 12 is here between two heat-dissipating windows / windows 15 stored. The focus of the imaging lens 20 is set so that the excitation light taking into account the thickness of the disc 15 correct in the fluorescent body 12 into being focused.

Advantageous for not exactly defined position of the replaceable head 16 is the parallel beam guidance through the interface between introduction part 3 and replaceable head 16 as they are in 6 is shown. At the distal end of the introducer 3 is a collimation lens 21 arranged, which from the light exit surface of the glass fiber 8th emerging excitation beams to infinity maps. In this case, the excitation light must be in the interchangeable head 16 arranged imaging lens 20 on the fluorescent body 12 be focused. The variant is more complex, but it allows greater tolerances in the attachment of the replaceable head 16 , With the collimated beam guidance, the greatest design options are open because the white light generation at any point in the replaceable head 16 can be provided.

In 7a is a larger fluorescent body 22 the deflection prism 17 downstream. In the fluorescent body 22 Therefore, the collimated excitation beam is irradiated. Because of the radiation density distributed over the beam cross section, the power density in the fluorescence body becomes 22 reduced. The reduction of the maximum radiation density advantageously reduces fading, aging and heating of the fluorescent body 22 , With sufficient intensity of the excitation beam, a part of the excitation light can also directly through the fluorescent body 22 as by the dotted continuation of the collimated excitation beam through the illumination beam cone 19 is indicated. Inside the white lighting beam cone 19 then appears on the observed object a z. B. bruise, which can be used as a marker. The scattering properties of the fluorescent body 22 must be adapted accordingly.

7b shows the same arrangement, but with forward lighting and observation.

According to the embodiment 8th becomes the collimated excitation beam through a beam splitter 23 split into two beams. The part reflected at the beam splitter surface is used for conversion to white light. From the transmitted part two parallel measuring beams are generated in a conventional manner on not further designated optical elements, which form a comparative scale for image measurement in the image. The at the beam splitter 23 The transmitted part of the excitation beam can also be used to excite another fluorescence body. By means of several individually excited fluorescence bodies, a shadow-free illumination is made possible, the reliability of the system is improved or different color spectra or emission directions can be set.

According to the embodiment 9a likewise a division of the collimated excitation beam occurs. The at the beam splitter 23 transmitted part is via a diffractive optical element 24 split into a plurality of radiation beams to produce a measurement pattern. The fluorescent body 12 is in this embodiment as a ball 25 represented by a transparent, heat-conducting pedestal 26 is held. The base 26 and the ball 25 be from a reflector 27 includes. The spherical shape ensures uniform radiation. The dissipation of heat is due to the small contact surface on the base 26 but unfavorable.

At the in 9b illustrated embodiment, the same lighting elements are provided as in 9a , However, for the observation of the illuminated object area here is a video camera 28 in the replaceable head 16 integrated, via contacts 29 electrically with the distal end of the introduction part 3 is connected. The spherical fluorescent body 25 is here in a reflector body 30 used, whose z. B. parabolic inner reflector surface is mirrored. The reflector body 30 may be around the spherical fluorescent body 25 around with a transparent heat conductor 31 filled out.

In the description of the embodiments, it was initially assumed that the transmission of a fluorescence exciting light wavelength through the glass fiber. However, it is also possible to feed into the optical fiber the light from more than one laser diode with different wavelengths of light. In the replaceable head 16 must then in the beam splitter 23 the beam splitter surface are provided with a dichroic coating which is transparent to the wavelengths of the radiation deviating from the excitation wavelength. As a result, a more favorable for the measuring radiation color, z. B. red or green, are used for better visibility.

• • Da zur Übertragung des Anregungslichtes im Prinzip nur eine einzige Glasfaser genügt, wird eine bessere Flexibilität des Einführungsteiles gegenüber Verbiegungen bei der Ablenkung des Distalendes erreicht. Die geringere Rückstellkraft einer Einzelfaser gegenüber den herkömmlichen Faserbündeln hat eine Verbesserung der Mechanik zur Folge, da die Einzelfaser viel biegsamer als ein Faserbündel ist. Durch die geringere Rückstellkraft wird der mechanische Ablenkungsvorgang am Distalende präziser.
• • Aufgrund des großen Durchmessers herkömmlicher Lichtleiterfaserbündel entstehen beim Biegen jeweils an den Innen- und Außenfasern Scherkräfte, die die Fasern ausreißen oder knicken können. Bei einer Einzelfaser entstehen keine Innen-Außen-Zugkräfte.
• • Der Einzelfaserdurchmesser beträgt mit Schutzmantel nur ca. 80–900 Mikrometer. In einem konventionell beleuchteten Videoendoskop beträgt demgegenüber der Kaltlicht-Bündeldurchmesser zwischen ca. 1 bis 3 mm. Ein Endoskop mit Einzelfaserübertragung des Anregungslichtes kann daher insgesamt mit einem wesentlich geringeren Querschnitt konstruiert werden.
• • Wenn eine Faser nicht ausreicht, können ohne wesentliche Querschnittserhöhung mehrere Fasern auf einen gemeinsamen Fluoreszenzkörper einstrahlen oder sie können jeweils einen eigenen Fluoreszenzkörper bestrahlen. Somit kann in einfacher Weise die Lichtleistung hochskaliert werden.
• • Wenn die Fluoreszenzquelle klein ist gegenüber der Strahlformungsoptik, kann die Ausleuchtung dem Gesichtsfeld optimal angepaßt werden.
• • Durch die Wahl des oder der Fluoreszenzfarbstoffe im Fluoreszenzkörper und/oder durch die Wahl des Anregungslichtes ist das Farbspektrum anpaßbar. So kann z. B. mit Anregung in UV und blau in der gleichen Faser das Spektrum an die zur Farbwiedergabe optimale Schwarzkörperstrahlung angepaßt werden. Es kann auch Licht zum Zwecke der Streuung ohne Nutzung des Fluoreszenzeffektes eingestrahlt werden. Dazu können verschiedene Lichtquellen z. B. mit einem Faserkoppler in eine Einzelfaser eingespeist werden. Durch Austauschen eines Wechselkopfes kann ebenfalls ein Spektrumswechsel erfolgen. Bei der Wahl des Anregungslichtes kann das Farbspektrum sogar während des endoskopischen Betrachtens geändert werden, was z. B. vorteilhaft ist bei Untersuchungen auf Farbveränderungen des Untersuchungsobjekts.
• • Ist der Fluoreszenzkörper durch Alterung ausgeblichen, gibt er nicht mehr seine maximale Helligkeit ab. Dann ist er z. B. via Austausch eines Wechselkopfes auswechselbar. Es ist auch möglich, nur den Beleuchtungskörper oder nur den Fluoreszenzkörper auszutauschen, wodurch dann ein Maximum an Wiederverwendung der Teile möglich wird. Dies spart Gebrauchskosten gegenüber fest eingebauten Fluoreszenzsystemen.
• • Weil die Laserdiode in der Versorgungseinheit als Receptacle ausgestaltet ist, kann sie bei Defekt mit dem Receptacle jederzeit ausgetauscht werden. Falls in Zukunft Laserdioden mit größerer Lichtleistung erhältlich sind, kann das endoskopische System jederzeit auf einfache Art aufgerüstet werden, womit die Lichtleistung am Distalende erhöht werden kann. Erfordern dann die höhere Leistung oder eine veränderte Wellenlänge eine Anpassung des Fluoreszenzkörpers, so ist das wegen der erfindungsgemäßen Austauschbarkeit möglich.
• • Durch die steckbare Verbindung der Übertragungsfaser zur Laserdiode und durch die Positionierung des Fluoreszenzkörpers als separates Bauteil ist die Faser jederzeit austauschbar. Dies ist ein wesentlicher Servicevorteil, da die Faser im Betrieb brechen oder reißen kann.
• • Bei Verwendung von energieeffizienten Laserdioden zur Speisung der Faser ist ein Batteriebetrieb möglich. Dadurch wird ein mobiler Einsatz des Systems erleichtert.
• • Durch den Einsatz von größeren Lasern ist die Übertragung von Lichtleistungen bis zu einigen Watt ans Distalende möglich. Die distal abgegebene Lichtmenge wird dann nur durch den Fluoreszenzkörper und dessen thermische Einbindung begrenzt. Durch die Einstrahlung hoher Intensitäten ist es auch möglich, nichtlineare Effekte auszunutzen.
• • In der Endoskopie stört oft der Effekt, daß bei langen flexiblen Endoskopen, z. B. ab 5 m, das Beleuchtungslicht mit zunehmender Länge zunehmend gelblich wird. Dies rührt von den stärkeren Lichtverlusten der kurzwelligen Spektralanteile in den Lichtleitern her. Wenn mit einem Laser angeregt wird, ist dagegen nur eine Wellenlänge vorhanden. Dadurch ist keine Veränderung des Anregungsspektrums mit der Länge möglich, so daß nach der Umwandlung auch das ausgestrahlte Licht seine Farbe weitgehend unabhängig von der Länge des Endoskops beibehält. Minimale Farbänderungen wegen nicht linearer Umwandlung lassen sich durch Leistungsanpassung bei Bedarf beheben.
• • Die Fasern für Laserübertragung weisen bei Einstrahlung des Laserlichts mit kleiner numerischer Apertur eine geringere Dämpfung auf als die üblicherweise verwendeten Weißlichtfasern, bei denen die Einstrahlung konventioneller Beleuchtung mit hoher numerischer Apertur erfolgt. Mit dem neuen Beleuchtungssystem sind daher wesentlich längere Endoskope möglich.
• • Die konventionellen Lichtquellen, wie z. B. Halogenlampen oder Gasentladungslampen, sind technisch an den physikalischen Grenzen angelangt. Bei den Laserdioden oder den Fluoreszenzkörpern ist jedoch zu erwarten, daß ihre Leistungen noch erhöht werden können. Die Technik des neuen Beleuchtungssystems wird daher von der Weiterentwicklung der Komponenten profitieren.
• • Die Intensität des Fluoreszenzlichts ist dimmbar, ohne daß sich die Farbe wesentlich ändert. Mechanische Teile, wie Blenden oder Absorber sind für eine Abschwächung nicht erforderlich. Eine einfache Reduktion des Anregungslichts reduziert entsprechend die Ausstrahlung des umgewandelten Lichts. Völlig farbneutrale Dimmung ist hingegen durch einfache Pulsweiten-Modulation möglich.
• • Bei Laserdioden kann durch Modulation des Laserstroms die Intensität des Anregungslichts schnell und mit wenig Aufwand verändert werden. Durch Unterbrechung oder Variation des Anregungslichts kann nahezu sofort z. B. das umgewandelte Licht ausgeschaltet werden. Es muß lediglich noch das extrem kurze Nachleuchten des Fluoreszenzkörpers abgewartet werden. Diese schnelle Modulierbarkeit ist bei Topografie-Meßaufgaben vorteilhaft, die nur kurzzeitig eine spezifische Meßbeleuchtung ohne Weißlichtbeleuchtung erfordern.
• • Die Montage des Endoskops wird vereinfacht, da keine Faserbäume eingezogen werden müssen.
• • Die Reparaturmöglichkeiten des Endoskops werden verbessert, da der Austausch einzelner Fasern einfacher ist als der Austausch eines Faserbündels.
• • Es entfallen die Probleme bei der Abdichtung der porösen Enden der Faserbündel gegen Eindringen von Flüssigkeiten.
• • Es ist eine Mehrwellenlängen-Anregung mit UV und blau in der gleichen Faser möglich, um z. B. das Spektrum an die Schwarzkörperstrahlung besser anzugleichen. Die Einspeisung in dieselbe Faser kann mit einem Faserkoppler nahezu verlustfrei erfolgen.

The advantages of the fiber-pumped fluorescence illumination can be summarized as follows:

• Since, in principle, only one single glass fiber suffices for the transmission of the excitation light, a better flexibility of the introduction part is achieved compared to deflections in the deflection of the distal end. The lower restoring force of a single fiber over the conventional fiber bundles results in an improvement of the mechanics, since the single fiber is much more flexible than a fiber bundle. The lower restoring force makes the mechanical deflection process at the distal end more precise.
• • Due to the large diameter of conventional fiber optic bundles, bending forces occur at the inner and outer fibers, which can rip or bend the fibers. In a single fiber no internal-external tensile forces.
• • The single fiber diameter with protective jacket is only approx. 80-900 microns. In contrast, in a conventionally illuminated video endoscope, the cold-light bundle diameter is between approximately 1 to 3 mm. An endoscope with single fiber transmission of the excitation light can therefore be constructed overall with a much smaller cross-section.
• • If one fiber is insufficient, several fibers can radiate onto a common fluorescence body without significant increase in cross-section, or they can each irradiate their own fluorescence body. Thus, the light output can be upscaled in a simple manner.
• • If the fluorescence source is small compared to the beam shaping optics, the illumination can be optimally adapted to the visual field.
• By the choice of the fluorescent dye (s) in the fluorescent body and / or by the selection of the excitation light, the color spectrum can be adapted. So z. B. with excitation in UV and blue in the same fiber, the spectrum are adapted to the optimal color reproduction blackbody radiation. Also, light may be irradiated for the purpose of scattering without using the fluorescence effect. For this purpose, various light sources z. B. be fed with a fiber coupler in a single fiber. By replacing a replaceable head can also be done a spectrum change. When choosing the excitation light, the color spectrum can be changed even during endoscopic viewing, which z. B. is advantageous in investigations on color changes of the examination subject.
• • If the fluorescence body is faded by aging, it no longer gives off its maximum brightness. Then he is z. B. interchangeable via exchange of a replaceable head. It is also possible to replace only the lighting fixture or only the fluorescent fixture, whereby then a maximum of reuse of the parts is possible. This saves on usage costs compared to permanently installed fluorescence systems.
• • Because the laser diode in the supply unit is designed as a receptacle, it can be replaced at any time in the event of a defect with the Receptacle. If laser diodes with greater light output are available in the future, the endoscopic system can be easily upgraded at any time, thus increasing the light output at the distal end. If the higher power or a changed wavelength then necessitate an adaptation of the fluorescent body, this is possible because of the exchangeability according to the invention.
• • The fiber is replaceable at any time thanks to the plug-in connection of the transmission fiber to the laser diode and the positioning of the fluorescence body as a separate component. This is a significant service advantage because the fiber can break or crack during operation.
• • When using energy-efficient laser diodes to feed the fiber, battery operation is possible. This facilitates a mobile use of the system.
• • The use of larger lasers allows the transmission of light outputs up to a few watts to the distal end. The amount of light emitted distally is then limited only by the fluorescence body and its thermal integration. Due to the irradiation of high intensities, it is also possible to exploit nonlinear effects.
• • In endoscopy often disturbs the effect that in long flexible endoscopes, eg. B. from 5 m, the illumination light becomes increasingly yellowish with increasing length. This is due to the stronger light losses of the short-wave spectral components in the optical fibers. When excited with a laser, however, only one wavelength is present. As a result, no change in the excitation spectrum with the length is possible, so that after the conversion and the emitted light retains its color largely independent of the length of the endoscope. Minimal color changes due to non-linear conversion can be corrected by adjusting the power as needed.
• • The laser transmission fibers have less attenuation when exposed to small numerical aperture laser light than the commonly used white-light fibers that emit conventional high numerical aperture illumination. The new lighting system therefore allows much longer endoscopes.
• • The conventional light sources, such as As halogen lamps or gas discharge lamps are technically reached the physical limits. In the case of the laser diodes or the fluorescent bodies, however, it is to be expected that their powers can still be increased. The technology of the new lighting system will therefore benefit from the further development of the components.
• • The intensity of the fluorescent light is dimmable without the color changing significantly. Mechanical parts such as diaphragms or absorbers are not required for attenuation. A simple reduction of the excitation light correspondingly reduces the radiation of the converted light. Completely color-neutral dimming is possible by simple pulse width modulation.
• • With laser diodes, the intensity of the excitation light can be changed quickly and with little effort by modulating the laser current. By interruption or variation of the excitation light can almost immediately z. B. the converted light are turned off. It only needs to wait for the extremely short afterglow of the fluorescent body. This rapid modulation is advantageous in topography measurement tasks that only require a specific measurement illumination without white light illumination for a short time.
• • Assembly of the endoscope is simplified because no fiber trees need to be retracted.
• • The repair possibilities of the endoscope are improved, since the replacement of individual fibers is easier than the replacement of a fiber bundle.
• • Eliminates the problems in sealing the porous ends of the fiber bundles against ingress of liquids.
• • It is possible a multi-wavelength excitation with UV and blue in the same fiber to z. B. to better match the spectrum of the black body radiation. The feeding into the same fiber can be done almost lossless with a fiber coupler.

LIST OF REFERENCE NUMBERS

1

Endoscopic system

2

eyepiece

3

introduction part

4

supply unit

5

Stimulating ray source

6

laser diode

7

coupling optics

8th

glass fiber

8a

thinned distal end of the fiberglass

9

Optical fiber cable

10

lighting

11

version

12

fluorescent body

13

Light opening

14

optical element

15

Heat-dissipating pane / window

16

change head

17

deflecting prism

18

Lighting Lens

19

Illumination beam cone

20

imaging lens

21

collimating optics

22

larger fluorescence body

23

beamsplitter

24

Diffractive optical element

25

spherical fluorescent body

26

Heat conductive base

27

reflector

28

video camera

29

electrical contacts

30

reflector body

31

transparent heat conductor

Claims (12)

Endoscopic system ( 1 ) in a proximal supply unit ( 4 ) arranged excitation radiation source ( 5 ), with an optical radiation transmission path in an insertion part ( 3 ) and a distal-side fluorescence converter, wherein as excitation radiation source ( 5 ) a laser diode emitting in the short-wave visible spectral range (US Pat. 6 ) and as optical transmission line a glass fiber ( 8th ) and the fluorescence converter is suitable for conversion into white light, and in which a fluorescence element (as fluorescence converter) ( 12 . 22 . 25 ) as a separate, exchangeable component of the light exit surface of the glass fiber ( 8th ), characterized in that the fluorescent body ( 12 . 22 . 25 ) in one to the introductory part ( 3 ) coupleable head ( 16 ) is arranged, wherein at the distal end of the insertion part ( 3 ) an imaging optics ( 21 ) for generating a collimated beam from the light exit surface of the glass fiber ( 8th ) Exiting excitation beam is arranged and the replaceable head ( 16 ) for generating a lighting and / or measuring beam with other optical components ( 14 . 17 . 18 . 20 . 23 . 24 . 27 . 30 ) and heat-dissipating components ( 15 . 26 . 31 ) is trained. Endoscopic system according to claim 1, characterized in that the fluorescent body ( 12 . 22 ) in the replaceable head ( 16 ) a heat dissipating window ( 15 ) is preceding or / and downstream. Endoscopic system according to claim 1, characterized in that the fluorescent body ( 12 . 22 ) between two heat-conducting windows ( 15 ). Endoscopic system according to claim 2 or 3, characterized in that at least one window ( 15 ) is designed as a diamond wheel or transparent, diamond-coated element. Endoscopic system according to claim 1, characterized in that in the replaceable head ( 16 ) an imaging lens ( 20 ) for focusing the collimated excitation beam onto the fluorescent body ( 12 . 22 ) is arranged. Endoscopic system according to claim 1, characterized in that in the replaceable head ( 16 ) an optical element ( 14 ) for adapting the radiation density of the collimated excitation beam to the geometric and fluorescence-optical properties of the fluorescent body ( 12 . 22 ) is arranged. Endoscopic system according to claim 1, characterized in that in the replaceable head ( 16 ) on the light entry side a beam deflecting element ( 17 ) is arranged. Endoscopic system according to claim 7, characterized in that the beam deflecting element ( 17 ) as a beam splitter ( 23 ) is trained. Endoscopic system according to claim 8, characterized in that the beam splitter ( 23 ) is designed as a cube element with beam-splitting and radiation-deflecting cemented surface. Endoscopic system according to claim 8, characterized in that in the supply unit ( 4 ) at least one further radiation source with emission in the red or green spectral range and for coupling into the glass fiber ( 8th ), the beam splitter ( 23 ) is provided with a dichroic coating for reflection or transmission of the further radiation. Endoscopic system according to claim 1, characterized in that the fluorescent body ( 12 . 22 ) light-emitting optical imaging means ( 14 . 18 ) is connected upstream for generating a light beam having a predetermined aperture. Endoscopic system according to claim 1, characterized in that the fluorescent body ( 12 . 22 . 25 ) around a transparent heat-conducting medium ( 31 ) is surrounded.

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