An optical coherence tomography system comprising a zoomable Kepler system.

专利摘要:
The invention relates to an optical system (1) for examining an eye by means of optical coherence tomography. The OCT system (2) is designed so that at least one first and one second state of the optical system can be selectively adjusted by means of a control of the variable optics (10). In the first state, the OCT measuring beam has a measuring focus at an object distance from the objective, wherein the object distance has a value between 50 millimeters and 400 millimeters. In the second state, the measuring beam has a defocusing at the same object distance, the defocusing corresponding to a distance of a virtual or real focus from a position of the object distance which is greater than 100 millimeters.
公开号:CH711778B1
申请号:CH00325/17
申请日:2015-09-21
公开日:2019-06-14
发明作者:Högele Artur；Steffen Joachim；Hauger Christoph；Matz Holger
申请人:Zeiss Carl Meditec Ag；
IPC主号:

专利说明:

Tabelle 1 [0161] Die optisch wirksamen Flächen der Konfigurationen, welche in den Fig. 6A bis 7C wiedergegeben sind, weisen die in der Tabelle 1 wiedergegebenen Krümmungsradien und Abstände auf. Wie mit Bezug auf die Fig. 5 dargelegt wurde, weist die zweite bewegbare optische Einheit 11 die optisch wirksamen Flächen S1 bis S5 auf. Die erste bewegbare optische Einheit weist die optisch wirksamen Flächen S6 und S7 auf. Die dritte optische Einheit weist die optisch wirksamen Flächen S8 bis S10 auf. Das Objektiv weist die optisch wirksamen Flächen S11 bis S13 auf.
Tabelle 2 [0162] Die Durchmesser der optisch wirksamen Flächen, die Materialien der optischen Elemente sowie die Brechzahl, welche diese Materialen bei einer Wellenlänge des Messstrahls von 1060 Nanometer aufweisen, sind in der Tabelle 2 wiedergegeben.
[0163] In der Konfiguration der Fig. 7B erzeugt die erste optische Komponente, welche aus der ersten bewegbaren optischen Einheit 11 und der zweiten bewegbaren optischen Einheit 12 besteht, innerhalb der variablen Optik weder einen reellen Fokus noch einen virtuellen Fokus. In der Konfiguration der Fig. 7B ist die variable Optik so konfiguriert, dass die Brennebenen-Position der Hauptebene des objektseitigen Strahlausgangs der ersten optischen Komponente ausserhalb der variablen Optik angeordnet ist. Hingegen ist in den Konfigurationen der Fig. 7A, 6A, 6B, 7A und 7C diese Brennebene innerhalb der variablen Optik angeordnet.
[0164] Diese grosse Verschiebbarkeit der Brennebenen-Position ermöglicht es, die Defokussierung des Messstrahls 9 in der Objektebene 40 an einen grossen Bereich an Fehlsichtigkeiten des Auges anzupassen. Insbesondere ist es dadurch möglich, den in der Fig. 7B dargestellten divergenten Messstrahl in der Objektebene 40 zu erzeugen, welcher eine Untersuchung von Augen erlaubt, welche eine Fehlsichtigkeit von -5 dpt aufweisen.
[0165] Die Fig. 8 illustriert den Aufbau der Kollektoroptik 22 für das OCT-System des in der Fig. 1 dargestellten optischen Systems 1. Die Kollektoroptik 22 weist eine veränderbare Brennweite auf. Die Brennweite der Kollektoroptik 22 ist so steuerbar veränderbar, dass für verschiedene Werte der Brennweite der Abschnitt 69 des Messstrahls 9, welcher von der Kollektoroptik 22 ausfällt, jeweils parallel ist. Für die verschiedenen Werte der Brennweite ist ein Durchmesser des Ab-
Schnitts 69 jeweils verschieden. Daher verursachen die verschiedenen Werte der Brennweite der Kollektoroptik verschiedene Werte der numerischen Apertur des auf den Messfokus 43 zulaufenden Abschnitts des Messstrahls 9.
[0166] Diese Ausführung der Kollektoroptik 22 ermöglichtes, die variable Optik für die Funktion der Verstellung der axialen Messfokus-Position zu optimieren, da die variable Optik nicht mehr die Funktion der Einstellung der numerischen Apertur übernehmen muss. Die Verschiebung des Messfokus entlang der Achse des Messstrahls wird dann durch die Ansteuerung der variablen Optik bewirkt, die Einstellung der numerischen Apertur des Messstrahls am Messfokus jedoch durch die Ansteuerung der Kollektoroptik bewirkt. Durch die Aufteilung dieser zwei Funktionen auf zwei getrennte optische Systeme können erweiterte Bereiche für die Einstellung der axialen Messfokusposition und/oder der numerischen Apertur erhalten werden. Des Weiteren wird dadurch ermöglicht, die variable Optik kompakter aufzubauen, wodurch eine Platzersparnis im Umgebungsbereich des Objektivs bewirkt wird. Des Weiteren wird dadurch erreicht, dass der Messstrahl 9 als paralleler Strahl durch das Scansystem 30 geführt wird, anstatt als konvergenter oder divergenter Strahl. Dadurch wird verhindert, dass die Bildqualität der OCT-Daten durch Doppler-Effekte beeinträchtigt wird, wenn die Scanspiegel nicht perfekt relativ zueinander ausgerichtet sind. Ferner wird dadurch vermieden, dass die Beziehung zwischen der Scanposition und dem Drehwinkel der Spiegel unterschiedlich ist für die Scanspiegel.
[0167] Die Fig. 8 zeigt den Aufbau der Kollektoroptik 22. Die Kollektoroptik 22 formt einen Abschnitt des Messstrahls, welcher aus der Lichtaustrittsfläche 25 der optischen Faser 23 austritt, in einen Abschnitt 69 des Messstrahls 9 um, welcher von der Kollektoroptik 22 ausfällt und welcher für verschiedene Werte einer einstellbaren Brennweite der Kollektoroptik 22 parallel ist.
[0168] Wie in der Fig. 8 gezeigt ist, weist die Kollektoroptik 22 eine erste bewegbare optische Einheit 72 und eine zweite bewegbare optische Einheit 73 auf. Die erste bewegbare optische Einheit 72 weist eine negative Brechkraft auf. Die zweite bewegbare optische Einheit 73 weist eine positive Brechkraft auf. Die zweite bewegbare optische Einheit 73 ist, gesehen im objektgerichteten Lichtweg des Messstrahls 9, stromabwärts der ersten bewegbaren Einheit 72 angeordnet. Durch die zweite bewegbare Einheit 73 verlässt der Messstrahl 9 die Kollektoroptik 22. Für verschiedene Werte der einstellbaren Brennweite der Kollektoroptik 22 ist der Abschnitt 69 des ausfallenden Messstrahls 9 jeweils parallel.
[0169] Die Kollektoroptik 22 weist eine dritte optische Einheit 71 auf, welche stromaufwärts der ersten bewegbaren Einheit 72 angeordnet ist. Die dritte optische Einheit 71 weist eine positive Brechkraft auf. Des Weiteren weist die Kollektoroptik 22 eine vierte optische Einheit 70 auf. Die vierte optische Einheit 70 ist stromaufwärts der dritten optischen Einheit 71 angeordnet und weist ebenfalls eine positive Brechkraft auf. Durch die vierte optische Einheit 70 tritt der Messstrahl 9 in die Kollektoroptik 22 ein. Ein Abschnitt 75 des Messstrahls 9, welcher von der vierten optischen Einheit 70 ausfällt, ist parallel. Zwischen der vierten optischen Einheit 70 und der dritten optischen Einheit 71 ist eine Blende 74 angeordnet.
[0170] Die Kollektoroptik 22 ist so konfiguriert, dass für verschiedene Werte der Brennweite der Kollektoroptik ein Durchmesser des Abschnitts 69 des Messstrahls 9, welcher von der Kollektoroptik 22 ausfällt, auf verschiedene Werte steuerbar einstellbar ist. Für die verschiedenen Werte des Durchmessers ist der Abschnitt 69 des Messstrahls 9, welcher von der Kollektoroptik 22 ausfällt, parallel. Dadurch sind verschiedene Werte der numerischen Apertur am Messfokus einstellbar,
wobei für jeden der verschiedenen Werte der Messstrahl 9 als paralleler Strahl durch die Scaneinrichtung 30 (gezeigt in der Fig. 1) durchtritt.
[0171] Die optisch wirksamen Flächen der Kollektoroptik 22, welche in der Fig. 8 wiedergegeben sind, weisen die in der Tabelle 3 wiedergegebenen Krümmungsradien, Abstände und Durchmesser auf. Ferner sind in der Tabelle 3 die Materialien der optischen Elemente sowie die Brechzahlen wiedergegeben, welche diese optischen Elemente bei einer Wellenlänge des Messstrahls von 1060 Nanometer aufweisen. Die erste bewegbare optische Einheit 72 weist die optisch wirksamen Flächen S20 und S21 auf. Die zweite bewegbare optische Einheit 73 weist die optisch wirksamen Flächen S22 und S23 auf. Die dritte optische Einheit 71 weist die optisch wirksamen Flächen S18 und S19 auf. Die vierte optische Einheit 70 weist die optisch wirksamen Flächen S15, S16 und S17 auf. Die vierte optische Einheit 70 kann als Kittglied ausgeführt werden.
[0172] Die Fig. 9A bis 9C zeigen drei Konfigurationen der Kollektoroptik 22, um unterschiedliche Durchmesser des parallelen ausfallenden Abschnitts 69 des Messstrahls zu erzeugen. Die in der Fig. 9A gezeigte Konfiguration der Kollektoroptik 22 erzeugt einen Durchmesser ρΊ mit einem Wert von 0,36 Millimeter. Die in der Fig. 9B gezeigte Konfiguration der Kollektoroptik 22 erzeugt einen Durchmesser p2 mit einem Wert von 0,72 Millimeter. Die in der Fig. 9C gezeigte Konfiguration der Kollektoroptik 22 erzeugt einen Durchmesser p3 mit einem Wert von 1,44 Millimeter.
[0173] Wie in der Fig. 1 gezeigt ist, weist das optische System 1 eine Fixierlichteinrichtung 87 auf zur Erzeugung eines reellen oder virtuellen Fixierpunktes für das Auge. Der reelle oder virtuelle Fixierpunkt ist durch den Patienten mit dem zu untersuchenden Auge 7 anblickbar, insbesondere wenn das Auge so positioniert ist, dass sich die Hornhaut in der Objektebene 40 befindet. Durch das Anblicken des Fixierpunktes erfolgt eine zentrale Fixierung des Fixierpunktes durch das Auge 7. Bei der zentralen Fixierung befindet sich das Bild des Fixierpunktes in der Foveolamitte des Auges 7. Mikrobewegungen des Auges werden hierbei vernachlässigt. Die Foveola ist das Gebiet des schärfsten Sehens innerhalb der Fovea. Der Durchmesser der Foveola beträgt etwa 0,33 Millimeter.
[0174] Der Fixierpunkt kann durch ein reelles oder virtuelles Bild definiert sein, welches durch die Fixierlichteinrichtung 87 erzeugt wird. Das reelle oder virtuelle Bild kann beispielsweise ein Fadenkreuz oder ein Kreis sein. Der Fixierpunkt kann dann beispielsweise das Zentrum des Fadenkreuzes oder das Zentrum des Kreises sein.
[0175] Die Fixierlichteinrichtung 87 umfasst eine Fixierlichteinheit 80. Die Fixierlichteinheit 80 weist eine Fixierlichtquelle auf, welche ein Fixierlicht 81 erzeugt, welches durch ein Umlenkelement 82 auf das Objektiv 29 gelenkt wird. Das Fixierlicht 81 durchsetzt das Objektiv 29. Es ist denkbar, dass das Fixierlicht auch die variable Optik 10 durchsetzt. Die Fixierlichtquelle kann beispielsweise eine LED und/oder einen Laser aufweisen. Das Fixierlicht 81 kann eine Lichtwellenlänge des sichtbaren Spektrums aufweisen, durch welche das Fixierlicht 81 für den Patienten gut vom Beleuchtungslicht einer Objektebenen-Beleuchtung (nicht gezeigt in der Fig. 1) des optischen Systems 1 unterscheidbar ist. Beispielsweise kann diese Lichtwellenlänge im grünen Spektralbereich liegen. Alternativ oder zusätzlich kann das optische System 1 so konfiguriert sein, dass sich die Intensität des Fixierlichts 81 entsprechend einem zeitlichen Muster verändert. Beispielsweise kann die Intensität des Fixierlichts 81 zeitlich periodisch an- und abschwellen, und/oder das Fixierlicht 81 kann zeitlich getriggert sein. Ein zeitlich getriggertes Fixierlicht kann beispielsweise ein blinkendes Fixierlicht sein.
[0176] Der reelle oder virtuelle Fixierpunkt, welcher von der Fixierlichteinrichtung 87 erzeugt wird, weist einen grossen Abstand von der Objektebene 40 auf. Daher erfolgt bei zentraler Fixierung des Fixierpunktes eine Ausrichtung der Sehachse des Auges 7 entlang einer definierten Sehachsenrichtung, und zwar im Wesentlichen unabhängig von der Position des Auges in einer Richtung senkrecht zur Sehachsenrichtung.
[0177] In dem optischen System 1, welches in der Fig. 1 dargestellt ist, ist das Fixierlicht 81 so konfiguriert, dass diese definierte Sehachsenrichtung parallel zur optischen Achse OA des Objektivs 29 verläuft. Ferner ist das OCT-System 2 so konfiguriert, dass die Achse des Messstrahls 9 entlang der optischen Achse OA des Objektivs 29 verläuft.
[0178] Dadurch wird eine präzise Vermessung der Vorderkammertiefe, der Linsendicke und der axialen Länge des Auges ermöglicht. Dies wird nachfolgend mit Bezug auf die Fig. 10A und 10B erläutert.
[0179] Die Fig. 10A zeigt das Auge 7 in einem Zustand, in welchem der Fixierpunkt zentral fixiert wird. Die Fixierungs-Sehachse des Auges, das heisst die Sehachse des Auges im Zustand der zentralen Fixierung, ist mit dem Bezugszeichen FA gekennzeichnet. In diesem Zustand befindet sich das Bild 79 des Fixierpunktes in der Foveolamitte 78. Die Fixierungs-Sehachse FA ist definiert als die Verbindungslinie zwischen der Foveolamitte 78 und dem Fixierpunkt, wenn sich das Auge im Zustand der zentralen Fixierung befindet.
[0180] Das Auge ist relativ zum optischen System so positioniert, dass bei einer Scaneinstellung des Scansystems eine Achse des einfallenden Abschnitts des Messstrahls 9 entlang oder im Wesentlichen entlang der Fixierungs-Sehachse FA verläuft. Dies ermöglicht es, durch OCT-Messungen eine Vielzahl anatomischer Parameter mit hoher Präzision zu ermitteln, wie beispielsweise die Vorderkammertiefe 82, die Linsendicke 83, der Abstand 84 zwischen der hinteren Linsenkapsel 85 und der Retina 77 sowie die axiale Länge 86 des Auges 7.
[0181] Die Fig. 10B stellt im Vergleich zur Fig. 10A das Auge in einem Zustand dar, in welchem der Fixierpunkt nicht zentral fixiert wird. Das Bild 79 des Fixierpunktes befindet sich dann ausserhalb der Foveolamitte 78. Wie an der Fig. 10B zu erkennen ist, weichen dann die entlang der Achse des Messstrahls 9 gemessenen Längen 88a, 89a, 90a und 86a ab von den in der Fig. 1OA dargestellten anatomischen Parametern der Vorderkammertiefe 82, der Linsendicke 83, des Abstandes 84 zwischen der hinteren Linsenkapsel 85 und der Retina 77, und der axialen Länge 86 des Auges 7.
[0182] Wie mit Bezug auf die Fig. 11A und 11B erläutert wird, ist das optische System so ausgebildet, dass der Zustand der zentralen Fixierung überprüfbar ist abhängig von OCT-Daten, welche von der Retina erfasst werden.
[0183] Die Fig. 11A zeigt einen ersten B-Scan, welcher einen Querschnitt durch die oberen Schichten 91, 92, 93, 94 der Retina wiedergibt. Die OCT-Daten der Fig. 11A wurden in dem Zustand erfasst, welcher in der Fig. 10A wiedergegeben ist, das heisst in einem Zustand, in welchem der Fixierpunkt durch das Auge zentral fixiert wird. Der B-Scan kann einen Teil eines Volumenscans repräsentieren. Der Querschnitt ist so konfiguriert, dass er das Bild der Foveolamitte enthält. Daher ist in dem B-Scan die Einsenkung 95 der Fovea zu erkennen, welche die Foveola repräsentiert Die Foveolamitte befindet sich bei einer Scanposition SP.
[0184] Die Fig. 11B zeigt einen zweiten B-Scan bei den gleichen Scanpositionen wie in der Fig. 11A. Die OCT-Daten der Fig. 11B wurden jedoch in dem Zustand des Auges erfasst, welcher in der Fig. 11B wiedergegeben ist, und in welchem der Fixierpunkt durch das Auge nicht zentral fixiert wird.
[0185] In den OCT-Daten, welche in der Fig. 11B wiedergegeben sind, erscheint daher an der Scanposition SP nicht die Foveolamitte, wie dies in den OCT-Daten der Fig. 11A wiedergegeben ist. Folglich ist anhand der OCT-Daten überprüfbar, ob sich das Auge in einem Zustand befindet, in welchem der Fixierpunkt zentral fixiert wird.
[0186] Das optische System ist ausgebildet, abhängig von den OCT-Daten zu bestimmen, ob sich das Bild der Foveolamitte an der Scanposition SP befindet und/oder ob eine Abweichung des Bildes der Foveolamitte von der Scanposition SP sich innerhalb einer vorbestimmten Grenze befindet. Dadurch ist es möglich, zu bestimmen, ob Parameter, welche durch Messungen am Auge erfasst wurden, innerhalb einer geforderten Genauigkeit liegen. Die OCT-Daten können einen zweidimensionalen Scan oder einen Volumenscan repräsentieren.
[0187] Die Scanposition SP kann beispielsweise dadurch bestimmt werden, dass OCT-Daten von der Retina über einen längeren Zeitraum erfasst werden, bei welchem das Fixierlicht aktiviert ist. Bei aktiviertem Fixierlicht befindet sich das Auge überwiegend in einem Zustand der zentralen Fixierung. Ist das Auge rechtsichtig und nicht akkommodiert, so ist die Scanposition SP diejenige, in welcher die Achse des auf das Auge einfallenden Abschnitts des Messstrahls parallel zur Fixierungs-Sehachse verläuft. In dem System, welches in der Fig. 1 dargestellt ist, ist dies dann die Scanposition, bei welcher der Messstrahl 9 entlang der optischen Achse verläuft.
[0188] Folglich wird durch das optische System in einfacher Weise ermöglicht, abhängig von OCT-Daten, welche von der Retina erfasst werden, den Zustand der zentralen Fixierung zu überprüfen.
[0189] Insbesondere können dadurch die in der Fig. 10A dargestellten anatomischen Parameter zuverlässig während einer Kataraktoperation bestimmt werden.
[0190] Bei der Überprüfung des Zustandes der zentralen Fixierung abhängig von den OCT-Daten muss sich der Messfokus nicht unbedingt im Bereich der Retina befinden. Es ist denkbar, OCT-Daten von auszumessenden anatomischen Strukturen innerhalb des Auges gleichzeitig mit OCT-Daten von der Retina zu erfassen. Eine solche anatomische Struktur kann beispielsweise die natürliche Linse sein. Der Messfokus kann sich hierbei ausserhalb der Retina befinden, wie beispielsweise in der natürlichen Linse oder im Bereich zwischen der natürlichen Linse und der Retina, wobei der axiale Messbereich jedoch bis zur Retina reicht.
[0191] Abhängig von den OCT-Daten kann dann einerseits die anatomische Struktur ausgemessen werden und andererseits geprüft werden, ob sich das Auge im Zustand der zentralen Fixierung befindet. Das optische System gemäss dem Ausführungsbeispiel erlaubt es hierbei, durch die Ansteuerung der variablen Optik und/oder durch die Ansteuerung der Kollektoroptik die axiale Position des Messfokus und/oder die numerische Apertur am Messfokus entsprechend zu konfigurieren.
[0192] Zur Vermessung der Augenlänge ist es alternativ auch denkbar, dass OCT-Daten zu unterschiedlichen Zeitpunkten zu erfassen, sodass die Daten unterschiedliche Zustände des Auges repräsentieren.
[0193] Bei entsprechender Wahl der Anzahl und der zeitlichen Distanz der unterschiedlichen Zeitpunkte repräsentieren dann die Messwerte die axiale Länge 86 (gezeigt in der Fig. 10A) im Zustand der zentralen Fixierung 86 und andererseits Messwerte in Zuständen, welche von der zentralen Fixierung abweichen, wie den Messwert 86a (gezeigt in der Fig. 10B). Es hat sich gezeigt, dass im Zustand der zentralen Fixierung die gemessenen Werte maximal sind. Werden also Messwerte über einen längeren Zeitraum erfasst, so repräsentieren die Maximalwerte die axiale Länge des Auges. Zur Erfassung von Vergleichswerten, in welchen das Auge sich nicht im Zustand der zentralen Fixierung befindet, kann das Fixierlicht ausgeschaltet werden.
Patentansprüche 1. Optisches System (1) zur Untersuchung eines Auges (7), wobei das optische System (1) aufweist: ein OCT-System (2), welches konfiguriert ist, einen Messstrahl (9) zu erzeugen, welcher auf das Auge (7) auftrifft;
description
Field of the Invention The present disclosure relates to an optical system for eye examination by means of optical coherence tomography. In particular, the present disclosure relates to a system for optical coherence tomography, which has a variable optics, by means of which a position of the measuring focus is controllably adjustable along its beam axis.
Background Optical coherence tomography (OCT) has evolved into a significant noninvasive eye diagnostic technique. Increasingly, this method is also involved in the operational process. OCT can produce sectional or volumetric images of the anterior and posterior portions of the eye at a comparatively high resolution and near real-time.
An example of the frequent use of OCT at the back of the eye is the diagnosis of glaucoma, macular changes and retinal diseases. For example, in the anterior segment, OCT is used for pre-, intra- and postoperative diagnostics in cataract surgery.
The variety of uses of OCT systems have led to the development of optical systems in which both a microscopy system and an OCT system is integrated. Such systems allow for OCT analysis in the field of view of the microscopy system so that the surgeon can navigate the OCT scan area using the microscopy system. The generated OCT images can improve the intraoperative orientation and diagnosis for the surgeon and therefore ensure an optimal course of the surgery.
Such optical systems typically can be operated in two configurations, the first configuration being for examining the anterior portion of the eye and the second configuration being for examining the retina. In the second configuration, an additional optical system is usually arranged in the beam path of the microscope and the OCT system between the objective and the eye.
In typical systems, this optic is a fundus imaging system or a contact lens. A fundus imaging system consists of an ophthalmoscope magnifier and a reducing lens. The ophthalmoscope magnifier creates an intermediate image of the retina between the reduction lens and the ophthalmoscope magnifier. With the help of a positioning device, the ophthalmoscope magnifier can be positioned so that the fundus of the eye is sharply imaged. Fundus imaging systems have the particular disadvantage that during surgery, unwanted eye contact can take place through the ophthalmoscope magnifier. In addition, possibilities to illuminate the surgical field by means of illumination from the surgical microscope are severely restricted when using the fundus imaging system. Usually, therefore, the illumination of the microscope system is turned off during operations in the rear section.
In contrast, contact lenses are fixed by means of a contact gel on the cornea. The contact glass causes the refractive power of the cornea to be canceled. This makes it possible to position the object plane of the microscope by a change in distance on the retina. During the operation, however, destabilization of the contact glass may occur. It can penetrate air bubbles, blood and fluid between the cornea and the contact lens. The consequence is that the surgical intervention must be interrupted in order to carry out a time-consuming cleaning process.
In fundus imaging systems as well as in contact lenses, a costly retrofit operation is required to switch between the configuration for imaging the anterior segment and the configuration for imaging the retina. Furthermore, when using these systems, the object plane of the microscope as well as the scanning plane of the OCT system are arranged together either only in the front portion of the eye or in the rear portion of the eye. However, there are surgical procedures in which it has been found advantageous to require examination of the retina by OCT, but the anterior segment of the eye should be further observed with the microscopy system. An example of such a surgical procedure is cataract surgery.
There is therefore a need for optical systems which allow efficient and accurate performance of an eye examination or procedure.
Summary Embodiments provide an optical system for examining an eye using optical coherence tomography (OCT). The system may include an OCT system configured to generate a measurement beam that impacts the eye. The OCT system may have a lens and variable optics. The variable optics may be located upstream of the objective, as viewed relative to an object-directed light path of the measurement beam.
The invention provides, on the one hand, an optical system for examining an eye, comprising an OCT system configured to generate a measuring beam which impinges on the eye; wherein the OCT system comprises a lens and a variable optics, wherein the variable optics, as seen relative to an object-directed light path of the measuring beam, upstream of the lens is arranged; wherein the variable optics comprises a first optical component having an optically effective entrance surface through which the measurement beam, in the object-directed light path, enters the variable optic and wherein the first optical component further comprises a focal plane of a main plane of an object-side beam exit of the first optical component ; wherein the variable optic is controllably configurable into a first configuration in which a focal plane position of the first optical component is within the variable optic; and wherein the variable optics is controllably configurable into a second configuration in which the position of the focal plane of the first optical component is outside the variable optics.
The invention, on the other hand, provides an optical system for examining an eye, comprising an OCT system configured to generate a measuring beam incident on the eye; wherein the OCT system comprises a lens and a variable optics, wherein the variable optics, as seen relative to an object-directed light path of the measuring beam, upstream of the lens is arranged; wherein the variable optics comprises a first optical component having an optically effective entrance surface through which the measurement beam, in the object-directed light path, enters the variable optic and wherein the first optical component further comprises a focal plane of a main plane of an object-side beam exit of the first optical component ; wherein the variable optic has a first configuration in which a position of the focal plane of the first optical component is within the variable optic; and wherein the first optical component has a controllably variable focal length.
The OCT system can be designed so that by means of a control of the variable optics or caused by the control of the variable optics, a first and a second state of the optical system are selectively adjustable. In the first state, the measuring beam may have a measuring focus at an object distance from the objective. The object distance can in the first and in the second state each have a value between 50 millimeters and 400 millimeters. In the second state, the measuring beam may have a defocusing at the same object distance. The defocus may correspond to a distance of a virtual or real focus from a position of the object distance which is greater than 100 millimeters. A measuring beam, which is parallel in the object plane, represents a distance of a virtual or real focus from the object plane, which is infinite, and therefore greater than 100 millimeters.
[0014] According to another embodiment, the distance of the real or virtual focus in the second state is greater than 130 millimeters, greater than 150 millimeters, greater than 170 millimeters, or greater than 200 millimeters, or greater than 300 millimeters, or greater than 500 millimeters , According to a further embodiment, the measuring beam in the second state at the object distance is parallel or substantially parallel. According to a further embodiment, the variable optics may be controllably adjustable so that the variable optics and the objective together form an afocal or a substantially afocal system. In the second state, the variable optics and the lens may together form an afocal or substantially afocal system.
In the first and in the second state, the object distance has an equal value. The eye, in particular the cornea of the eye or the front surface of the cornea, can be arranged at the object distance. The object distance may define a position relative to the lens and / or a position on the object side of the lens. The position of the object distance may be measured relative to a fixed reference point. Alternatively or additionally, a position of the objective measured relative to the fixed reference point, in the first and in the second state may be the same or substantially the same. The object distance may be measured along an optical axis of the objective and / or relative to an object-side vertex of the objective. The object distance may have a value in a range between 50 millimeters and 300 millimeters, or in a range between 100 millimeters and 300 millimeters or in a range between 100 millimeters and 250 millimeters, or in a range between 150 millimeters and 250 millimeters. For example, the object distance may be 150 millimeters or 200 millimeters or 250 millimeters.
Thereby, an optical system is provided, which allows an efficient and precise examination of the eye. In particular, OCT data from both the anterior portion of the eye and the posterior portion of the eye, such as the retina, can be detected within a short time. The conjunctiva, the cornea, the lens and the iris can be counted towards the anterior portion of the eye. Neither the use of a contact glass nor the use of a fundus imaging system is necessary for the examination of the posterior segment. The optical system can be configured such that in the first state a measuring focus of the measuring beam is arranged in the cornea of the eye and / or that in the second state the measuring focus is arranged in the retina of the eye. The cornea may be arranged at the position of the object distance. The eye may be a right eye in an unaccommodated state.
The measuring focus of the measuring beam may have a beam waist. The beam waist can be defined as the axial position along an axis of the measurement beam at which the measurement beam has the smallest diameter. The measuring focus, in particular the beam waist of the measuring focus, can be located within the axial measuring range of the OCT system. The axial measuring range can be an area along the beam axis of the measuring beam, via which scattering intensities can be detected during a scan of the OCT system. The acquisition of measurement data on the axia len measuring range can be done for example by changing the optical path length of the reference arm. The change in the optical path length of the reference arm, for example, by a change in position of a reference mirror, which is arranged in the reference arm.
Furthermore, the OCT system enables a combination with another optical component in an efficient manner. Such another optical component may be configured to generate a light beam or a beam path that passes through the lens. The light beam or the beam path may be directed to the eye. The further optical component may be, for example, a microscope or an aberrometer.
The OCT system may be a time-domain OCT system (TD-OCT) and / or a frequency-domain OCT system (FD-OCT). The OCT system may be a spectral-domain OCT system (SD-OCT) and / or a swept-source OCT system (SS-OCT).
The variable optics can be designed so that a transition between the first state and the second state by the driving of the variable optics can be generated. In other words, changing optical properties, other components of the OCT system, such as focal lengths, focal plane positions, refractive indices, and / or radii of curvature, may not be required to switch between the first state and the second state.
The optical system may include a controller. The controller may be in signal communication with the variable optics. Depending on control signals, which are transmitted from the controller to the variable optics, the control of the variable optics can take place.
The lens may have a focal length which is greater than 100 millimeters, or greater than 150 millimeters, or greater than 200 millimeters. The focal length of the lens may be less than 500 millimeters, or less than 400 millimeters, or less than 300 millimeters. The lens may have a variable focal length. The position of the object distance can be a focal plane of the objective in the first and in the second state.
In the first state, the measuring focus is arranged at the object distance. The beam waist of the measurement focus can be located at the object distance. The position of the measurement focus or the real or virtual focus can be measured without the presence of the eye or an object. The distance of the real or virtual focus thus represents a distance through air.
The phrase that a component is configured to controllably adjust a parameter of the component may be defined in the context of the present disclosure as meaning that the optical system has a controller that is in signal communication with the component. The controller may be configured to adjust the parameter depending on control signals to the component.
The OCT system may include an interferometer. The OCT system may be configured to generate the measurement beam and a reference beam. The OCT system may be configured to cause the measuring beam to interfere with the reference beam. The optical system can be designed so that the interference with a detector of the OCT system can be detected.
The OCT system may further be configured such that an axial measuring range in the first state is different from the axial measuring range in the second state. In the first state, the measuring focus can be arranged in the axial measuring range. In the second state, the retina of the eye can be in the axial measuring range. The change in the axial measuring range may include a change in the optical path length of the reference beam and / or the measuring beam.
A portion of the measuring beam may extend in a light guide. The light guide may be an optical fiber. The optical fiber may be a multimode fiber and / or a monomode fiber. The light guide can have a light emission. The light guide can be designed so that the measuring beam emits through the light exit into a measuring beam optics. The light emission can therefore form a light entry into the measuring beam optics. The measuring beam optics can be an imaging optic. The light entrance can therefore be a transition between a non-imaging optics and an imaging optics. The measuring beam optics can be designed and / or configured such that an image of the light entrance can be generated in the object area. The object area can be in the eye. The measuring focus of the measuring beam can be an image of the light entry. Alternatively or additionally, the real or virtual focus whose distance from the position of the object distance represents the defocusing, be an image of the light entrance. The measuring beam optics may include the variable optics and the objective. The measuring beam optics may comprise one or a combination of the following components: a scanning system, a collector optics and a deflection element.
The variable optics may comprise lenses, cemented members and / or mirrors. An optical axis extending through the variable optics may be rectilinear or angled.
The variable optics may be arranged upstream or downstream of a deflecting element relative to an object-directed light path of the measuring beam. The deflecting element may have a mirror and / or a beam splitter. An axis of a portion of the measuring beam which is incident from the deflecting element may run parallel or substantially parallel to the optical axis of the objective. The axis of the precipitating portion may be along or substantially along the optical axis of the objective.
According to a further embodiment, the optical system further comprises a scanning system. The scanning system can be designed for one-dimensional or two-dimensional scanning of the measuring beam or of the measuring focus. The measuring focus can be in the eye. Scanning may be a lateral scanning, that is scanning perpendicular to an axis of the measuring beam. The scanning system can be configured to scan the measurement focus, in particular the beam waist, in a scan plane. The scan plane may extend perpendicular or substantially perpendicular to the axis of the measurement beam. The scanning system can have one, two or more scan mirrors. Each of the scanning mirrors may be controllably pivotable about one or two axes. The variable optics may be configured to image a point on the deflection element, this point being located on a scanning mirror of the scanning system in at least one scanning position of the scanning system. Alternatively, this point may be at the at least one scanning position on the axis of a portion of the measuring beam which extends between two scanning mirrors of the scanning system.
The scanning system may be located upstream of the lens relative to an object-directed light path of the measuring beam. Additionally or alternatively, the scanning system may be located upstream or downstream of the variable optics. The scanning system can be arranged upstream or downstream of the deflecting element. The scanning system can be arranged downstream of the light entry into the measuring beam optics and / or downstream of the light exit from the light guide. The scanning system may be located upstream or downstream of the collector optics.
The OCT system may be configured such that in the first and / or in the second state of the measuring beam parallel or substantially parallel incident on the scanning system. In the first and / or in the second state, the measuring beam can be incident on the variable optics in parallel or substantially parallel to the light source side. Alternatively, the measuring beam in the first and / or second state light source side converge convergent or divergent. The OCT system can be designed so that the measuring beam controllable incident parallel, convergent or divergent to the variable optics.
According to a further embodiment, a total optical effect, which the measuring beam experiences on the way, which extends from a failure of the variable optics up to an incidence at the object distance, in the first state is the same or substantially the same as in the second State. The total optical effect can be understood as the change in the wavefront of the measuring beam at the end of the path compared with the wavefront at the beginning of the path. According to a further embodiment, the total optical effect which the measurement beam experiences along the way, which extends from a failure of the objective to an incidence at the object distance, is the same or essentially the same in the first state as in the second state. According to a further embodiment, the total optical effect which the measuring beam experiences along the way, which extends from a failure of the objective to an incidence at the object distance, is zero or essentially zero in the first and in the second state. According to a further embodiment, the measuring beam extends in the first and in the second state on the way, which extends from the failure of the lens to the incident at the object distance, by air. In the first state and in the second state, a total optical effect along a path, which starting from the light entry into the measuring beam optics, starting from the light exit from the optical fiber and / or starting from the incidence on the collector optics up to the incidence on the variable optics extends, be the same or substantially the same in the first state as in the second state. A focal length and / or a focal plane position of one or both of the main planes of the objective may be the same or substantially the same in the first state as in the second state. The combined optical effect of all optically active surfaces of the objective, which are penetrated by the measuring beam, can be described in the context of the paraxial optics by these two main planes of the objective.
The optical subsystem of that optical path, which extends from a failure of the variable optics until incidence on the object distance, may have a main plane of an object-side beam output and a main plane of a light source side beam input. The combined optical effect of all optically active surfaces of this optical subsystem, which are penetrated by the measuring beam can be described in the paraxial optics through these two main levels. The optical subsystem can consist, for example, of the deflecting element and the objective. In the first and in the second state, the focal length and / or the focal plane position of the main plane of the object-side beam exit and / or the focal length and / or the focal plane position of the light source-side beam input may have the same or essentially the same value. The focal plane position can be measured relative to a fixed reference point.
Embodiments provide a system for examining an eye using optical coherence tomography. The optical system may include an OCT system configured to generate a measurement beam which impinges on the eye. The OCT system may have a lens and variable optics. The variable optics may be located upstream of the objective, as viewed relative to an object-directed light path of the measurement beam. The OCT system may be designed so that at a same object distance from the lens, by means of a control of the variable optics or caused by the control of the variable optics, the measuring beam optionally (a) is substantially parallel or parallel adjustable; or (b) is adjustable to a defocus, which corresponds to a distance of a real or virtual focus of the measurement beam from the object distance, which is less than 300 millimeters. The object distance has the same value in the setting (a) and in the setting (b). The object distance in the setting (a) and the setting (b) can have a value between 50 millimeters and 400 millimeters.
Thereby, an optical system is provided, by which it is possible to examine the retina, both in right eyes, as well as eyes with ametropia. The refractive error can be a spherical refractive error. Defective vision can be measured in diopters. The greater the amount of ametropia, the less the distance of the real or virtual focus from the position of the object distance must be in order to produce a measurement focus on the retina when the cornea of the eye is located at the object distance.
If the distance of the virtual or real focus is greater than the object distance by 200 millimeters, the measuring beam can be focused on the retina in eyes with a defective vision of +5 dpt. If the distance of the virtual or real focus from the objective is 200 millimeters less than the object distance, the measuring beam can be focused on the retina in eyes with a defective vision of -5 dpt. The position of the object distance measured relative to a fixed reference point may be the same or substantially the same in the setting (a) and in the setting (b). Alternatively or additionally, a position of the lens measured relative to the fixed reference point, in the setting (a) and the setting (b) may be the same or substantially the same.
According to another embodiment, the distance of the real or virtual focus in the setting (b) may be less than 200 millimeters, or less than 180 millimeters, or less than 150 millimeters, or less than 130 millimeters, or less its as 100 millimeters, or less than 80 millimeters, or less than 70 millimeters. In the setting (a) and / or in the setting (b), the measuring beam can each incident parallel or substantially parallel to the variable optics. The optical system may include a scanning system. The OCT system may be designed so that in the setting (a) and / or in the setting (b), the measuring beam incident on the scanning system parallel or substantially parallel.
The optical system can be designed so that by means of the control of the variable optics, the defocusing at the object distance is continuously and / or discretely adjustable over a Defokussierungsbereich. The defocus range may include the settings (a) and / or (b). The driving of the variable optics can cause the discrete and / or the continuous adjustment.
The variable optics can be designed so that a transition between the setting (a) and the setting (b) by the control of the variable optics can be generated. In other words, the change of optical properties of other components of the OCT system may not be required to change between setting (a) and setting (b). According to a further embodiment, a total optical effect, which the measurement beam experiences on the way, which extends from a failure of the variable optics to an incidence at the object distance, in the setting (a) is equal to or substantially the same as in the setting (b). According to a further embodiment, the total optical effect which the measuring beam along the path, which extends from a failure of the objective up to incidence at the object distance, in the setting (a) is the same or substantially the same as in the setting (b ). According to a further embodiment, the total optical effect which the measurement beam experiences on the way, which extends from the failure of the objective to the incidence at the object distance, in the setting (a) and the setting (b) is zero or substantially zero. According to a further embodiment, the measuring beam in the setting (a) and the setting (b), starting from the failure of the lens to the incident at the object distance, by air. A focal length and / or a focal plane position of one or both of the main planes of the objective may be the same as or substantially the same as setting (b) in the setting (a).
In the setting (a), a total optical effect, which the measuring beam experiences on the way, which starting from the light exit from the light guide, starting from the light entering the measuring beam optics and / or starting from the incidence on the collector optics until for incidence on the variable optics, be the same or substantially the same as in the setting (b).
The optical subsystem of that optical path, which extends from a failure of the variable optics until incidence on the object distance, may have a main plane of an object-side beam output and a main plane of a light source side beam input. The combined optical effect of all optically active surfaces of the optical subsystem, which are penetrated by the measuring beam can be described in the context of paraxial optics through these two main levels. The optical subsystem can consist, for example, of the deflecting element and the objective. In the setting (a) and the setting (b), the focal length and / or the focal plane position of the principal plane of the object-side beam output and / or the principal plane and / or the focal plane position of the light-source-side beam input may have the same or substantially the same value ,
According to a further embodiment, by means of the control of the variable optics, the defocusing at the object distance further selectively adjustable so that the distance of the real or virtual focus from the lens between 50 millimeters and 150 millimeters is greater than the object distance, or between 25 millimeters and 150 mm greater than the object distance, or between 20 mm and 150 mm greater than the object distance.
The control of the variable optics can cause the distance of the real or virtual focus. The distance of the real or virtual focus from the objective may be measured along the optical axis of the objective and / or relative to an object-side vertex of the objective.
Embodiments provide an optical system for examining an eye. The system may include an OCT system. The OCT system may be configured to generate a measuring beam which impinges on the eye. The OCT system may have a lens, variable optics, and collector optics. The variable optics can be arranged in the measurement beam between the objective and the collector optics. The collector optics can have a controllably variable focal length. By means of the controllably variable focal length or caused by the controllable variable focal length, a diameter of a portion of the measuring beam, which fails of the collector optics, be changeable. The portion of the measuring beam may be parallel or substantially parallel before and after the change in the diameter. The OCT system may be designed such that defocusing of the measurement beam at a same object distance from the objective can be controllably adjusted by means of a control of the variable optics or caused by the activation of the variable optics. The object distance can have a value between 50 and 400 millimeters.
The defocusing can be measured as a distance of a real or virtual focus of the measuring beam from a position of the object distance. In other words, the distance of the real or virtual focus of the measuring beam from the position of the object distance is controllably adjustable by means of the control of the variable optics or caused by the control of the variable optics.
A ratio of a maximum value (ömax) of the diameter of the portion of the measuring beam, which fails of the collector optics, to a minimum value (δπίη) of the diameter (ie the value δΠ3Χ / δπίη), wherein the diameter by means of or caused by a control of Collector optics are adjustable, can be greater than 1.5, greater than 1.7, or greater than 1.8, or greater than 2 or greater than 3 or greater than 3.5. The ratio may be less than 10 or less than 20 or less than 30.
The collector optics may have a main plane of a light source side beam input and a main plane of an object side beam output. The combined optical effect of all optically active surfaces of the collector optics, which are penetrated by the measuring beam, can be described in the context of paraxial optics through these two main levels. The collector optics may be configured such that before and after the controllable change of the focal length, a position of a focal plane of the main plane of the light source side beam input is equal or substantially equal. At the position of the focal plane, a light entry into the OCT-measuring beam optics may be arranged. At the position of the focal plane, a light exit of a light guide of the OCT system can be arranged.
According to a further embodiment, the OCT system has a scanning system, which is located in the measuring beam between the collector optics and the variable optics. The OCT system may be configured so that a portion of the measuring beam that arrives at the scanning system is parallel or substantially parallel, or is adjustable in parallel or substantially parallel. The section of the measuring beam arriving at the scanning system may be parallel or substantially parallel for the different settings of the defocusing at the object distance, which are adjustable by means of or caused by the control of the variable optics.
According to a further embodiment, the collector optics has a first movable optical unit which has a negative refractive power.
In the context of the present disclosure, the term refractive power may refer to a spherical refractive power. In addition to the spherical power, one or no cylindrical power may be present. The refractive power may be a local refractive power or a non-local refractive power. The refractive power can be generated by means of rotationally symmetrical spherical and / or rotationally symmetrical aspherical optically effective surfaces. The optically effective surfaces which generate the refractive power may have one or more optically effective surfaces which have a cylindrical refractive power. The optically effective surfaces which generate the refractive power may be free of a cylindrical refractive power and / or free of aspherical surfaces. Further, in the present disclosure, the terms first, second, third and fourth optical units or movable optical units are used to distinguish the units from each other. For example, the term "third optical unit" does not indicate that there must be a first and a second optical unit.
In the context of the present disclosure, a movable optical unit may be defined as a component in which all optically active surfaces of the component are moved together as a unit while maintaining their arrangement relative to each other. In other words, the optically effective surfaces of the movable unit in the joint movement do not perform relative movement relative to each other.
One or more of the movable optical units may be configured to make a movement along and / or obliquely to an optical axis of the collector optics. For example, the collector optics may include one or more Alvarez lenses. Alternatively or additionally, one or more of the movable optical units may be configured to be selectively insertable and removable in the measuring beam.
Alternatively or additionally, the collector optics may comprise one or more optical units which have a controllably changeable shape of a refractive or reflective surface and / or a controllably variable refractive index. An optical unit may, for example, be one or a combination of a lens, a cemented element and a mirror. For example, the collector optics may have one or more liquid lenses.
According to a further embodiment, the collector optics on a second movable optical unit. The second movable optical unit may have a positive refractive power. The measuring beam can leave the collector optics in the object-directed light path through the second movable optical unit. In other words, the second movable optical unit can have an optically effective exit surface through which the measuring beam emerges from the collector optics in the object-directed light path.
According to a further embodiment, the collector optics on a first and a second movable optical unit. The first movable optical unit may have a negative refractive power and the second movable optical unit may have a positive refractive power. Seen along an object-directed light path of the measuring beam, the second movable optical unit can be arranged downstream of the first movable optical unit.
According to a further embodiment, the collector optics has a third optical unit. The third optical unit can be arranged upstream of a first movable optical unit of the collector optics, as seen relative to an object-directed light path of the measuring beam. The first movable optical unit may have a negative refractive power. Alternatively or additionally, the third optical unit may be arranged upstream of a second movable optical unit of the collector optics. The second movable optical unit may have a positive refractive power. Alternatively or additionally, the third optical unit may be arranged between the first movable optical unit and a fourth optical unit. Alternatively or additionally, the third optical unit may be arranged between the second movable optical unit and the fourth optical unit. Alternatively or additionally, the third optical unit may have a positive refractive power.
According to a further embodiment, the collector optics has a fourth optical unit. The fourth optical unit may be disposed upstream relative to an object-directed light path of the measuring beam, upstream of a first movable optical unit of the collector optics. The first movable optical unit may have a negative refractive power. Alternatively or additionally, the fourth optical unit may be arranged upstream of a second movable optical unit of the collector optics. The second movable optical unit may have a positive refractive power. Alternatively or additionally, the fourth optical unit can be arranged upstream of a third optical unit of the collector optics. The third optical unit may have a positive refractive power. Alternatively or additionally, a portion of the measuring beam which fails in the object-directed light path from the fourth optical unit may be parallel or substantially parallel. Alternatively or additionally, the fourth optical unit may have a positive refractive power. Alternatively or additionally, the measuring beam can enter the collector optics in the object-directed light path through the fourth optical unit. In other words, the fourth optical unit can have an optically effective entry surface through which the measurement beam, in the object-directed light path, enters the collector optics. All refractive surfaces of the collector optics, which are penetrated by the measuring beam, may be represented by the surfaces of the first movable optical unit, the second movable optical unit, the third and the fourth optical unit.
Embodiments provide an optical system for examining an eye. The system may include an OCT system configured to generate a measurement beam that impacts the eye. The OCT system may have a lens and variable optics. The variable optics may be located upstream of the objective, as viewed relative to an object-directed light path of the measurement beam. The variable optics may include a first optical component. The first optical component can have an optically effective entry surface through which the measurement beam, in the object-directed light path, enters the variable optics. The first optical component may include a focal plane of a principal plane of an object-side beam output of the first optical component. The variable optic may have a first configuration and / or be controllably configurable into a first configuration, wherein in the first configuration there is a focal plane position of the first optical component within the variable optic. Alternatively or additionally, the variable optics may be controllably configurable into a second configuration. In the second configuration, the position of the focal plane of the first optical component may be outside the variable optics. The first optical component may have a controllably variable focal length. By means of or caused by the controllably variable focal length, the variable optics can be switchable between the first and the second configuration. The controllably variable focal length may be a focal length of a principal plane of the object-side beam output of the first optical component. Alternatively or additionally, a plurality of different focal plane positions may be adjustable by means of or caused by the controllable variable focal length of the first component for a main plane of an object-side beam output of the variable optics. Alternatively or additionally, a defocusing of the measuring beam at the object distance can be adjustable by means of or caused by the controllably variable focal length of the first component. Alternatively or additionally, by means of or caused by the controllably variable focal length of the first component, the optical system between the first and the second state can be switched. In the first configuration of the variable optics, in the second configuration of the variable optics, in the first state of the optical system and / or in the second state of the optical system, the measurement beam may arrive parallel or substantially parallel to the variable optics.
The first optical component may include a main plane of an object-side beam output and a main plane of a light source-side beam input. The combined optical effect of all optically active surfaces of the first optical component, which are penetrated by the measuring beam, can be described in the context of the paraxial optics through these two main planes. The focal plane position and / or the focal length of a principal plane of the object-side beam output of the first optical component may be controllably variable.
The optically effective entrance surface may be, for example, the surface of a lens, a cemented element or a mirror. In other words, the first optical component has an optically active surface through which the measuring beam enters the variable optics in the object-directed light path. Optically effective surfaces can be, for example, refractive or reflective surfaces.
In the first configuration, the focal plane position of the first optical component is disposed within the variable optic. The focal plane position may be a position of a real focus, which is generated when a parallel beam is incident on the variable optics. The real focus can be arranged between two optical elements or within an optical element.
The term "within the variable optics" may be defined such that the focal plane position is located on the optical axis between a vertex of the optically active entrance surface and a vertex of an optically effective exit surface of the variable optic. The optically effective entrance surface and exit surface may be defined relative to the object-directed light path. The measuring beam can exit in the object-directed light path through the optically effective exit surface of the variable optics. In the first configuration, the measuring beam can form a real focus within the variable optics. The real focus of the measuring beam can be arranged between two optical elements or within an optical element. An optical element may, for example, be a lens or a cemented element.
In the second configuration, the focal plane position of the object-side principal plane of the first optical component is located outside the variable optics. According to one embodiment, in the second configuration, the focal plane of the first optical component is located on the object side of the variable optics. The second configuration of the variable optics can be designed such that with an incident parallel beam or with an incident parallel beam, this beam or beam traverses the variable optics without forming a real focus within the variable optics. The measuring beam in the second configuration does not necessarily have to be parallel to the variable optics.
The first optical component may consist of one or more optically active surfaces. In particular, the first optical component can consist of one or more lenses and / or cemented elements. The first optical component may comprise a first and / or a second movable optical unit. The first movable optical unit may have a negative refractive power. The second movable optical unit may have a positive refractive power. The second movable optical unit may be disposed upstream of the first movable optical unit, as viewed relative to the object-directed light path of the measuring beam.
According to one embodiment, in the first state of the optical system, the variable optic is in the first configuration. According to a further embodiment, in the second state of the optical system, the variable optic is in the second configuration.
A transition from the first variable optics configuration to the second variable optics configuration may include controllably varying the variable focal length of the first component. Alternatively or additionally, a transition from the first state of the optical system to the second state of the optical system may comprise controllably varying the variable focal length of the first component. The controllably variable focal length may be the focal length of a principal plane of an object-side beam output of the first component. According to a further embodiment, the variable focal length of the first component in the second configuration is greater, or greater than 1.5 times, or greater than twice or greater than 2.5 times or greater than three times that in the first configuration.
According to one embodiment, in the first configuration, the variable optic is an afocal or a substantially afocal system.
According to a further embodiment, the variable optics on a second optical component. The second optical component may be disposed downstream of the first optical component relative to an object-directed light path of the light beam. The second optical component may have a positive refractive power. The second optical component may be configured such that in the first configuration it images a point on the focal plane position of the focal plane of the first optical component on the object side towards infinity or substantially infinity. The second optical component, as seen relative to the object-directed light path, have the optically effective exit surface of the variable optics. In other words, the measuring beam can leave the variable optics in the object-directed light path through the optically effective exit surface.
According to one embodiment, in the first configuration, a focal length of a principal plane of a light source side beam input of the second optical component is greater than or greater than 1.5 times, or greater than 2 times, or greater than 2.5 times, or greater than a 3 times, or as a 4 times, the focal length of the main plane of the object-side beam output of the first optical component.
The second optical component may include a main plane of an object-side beam output and a main plane of a light-source-side beam input. The combined optical effect of all optically effective
Surfaces of the second optical component, which are penetrated by the measuring beam, can be described in the context of the paraxial optics by these two main planes.
According to a further embodiment, the optical system has a fixing light device. The fixation light device can be configured to generate a fixation point for an eye, wherein the eye, in particular a cornea of the eye, is arranged at the position of the object distance from the objective. The object distance can have a value between 50 millimeters and 400 millimeters.
A fixation point may be defined as an object point which is viewable by the eye. By looking at the fixation point is fixed centrally. The central fixation creates an image of the fixation point in the foveola center. Generating the fixation point may include generating a real or virtual image. The real or virtual image may define or contain the fixation point.
According to another embodiment, the fixing light means is adapted to generate a fixing light incident at the position of the object distance. The fixing light may be defocused at the position of the object distance. The defocusing of the fixation light may correspond to a distance of a real or virtual image plane from the position of the object distance which is greater than 100 millimeters or greater than 200 millimeters or greater than 300 millimeters. The real or virtual image and / or the real or virtual fixation point may be in the image plane. The fixation light can enforce the lens and / or the variable optics.
The optical system may be configured such that when the scan system is scanned, an axis of a portion of the measurement beam incident at the object distance is parallel or substantially parallel to the visual axis of the eye, the eye being at the object distance and the fixation point fixed centrally.
The visual axis may be defined as the connecting line between the fixation point and the image point of the fixation point on the retina, the fixation point being fixed centrally by the eye. The pixel is then in the foveola center. Alternatively or additionally, the visual axis may be defined or substantially defined by a direction of light rays of the fixation light at the object distance, ie at a position at which the light rays impinge on the cornea of the eye.
According to another embodiment, the optical system comprises a microscopy system which is configured to generate an observation channel. With the help of the observation channel, an image can be generated in an image plane of an object region of the eye, which is arranged in an object plane. The observation channel can enforce the lens. The object plane may be at the position of the object distance. The object plane may be optically conjugate to the image plane. The object plane may be a focal plane of the lens. The optical system can be designed so that radiation beams of the observation channel, which emanate from a point in the object plane, are imaged by the objective to infinity or essentially to infinity. In other words, the beams may be parallel or substantially parallel downstream of the lens. The variable optics may be free of light rays used to form an image in an image plane of the object area in the object plane. In particular, the variable optics can be arranged outside of a left and a right stereoscopic observation channel of the microscopy system. In particular, the variable optics can be penetrated only by the measuring beam and / or by light beams of a fixing light.
Since the object plane is located at the object distance, and variable defocusing at the object distance is adjustable by the variable optics, a surgeon can observe the anterior portion of the eye continuously with the microscope, while with the OCT system, tissue structures in both the anterior portion of the eye and can be examined in the posterior section of the eye. In particular, the OCT system can measure the axial length of the eye, while areas of the front section can be continuously imaged by the microscope system. It has been shown that this is particularly advantageous in the performance of cataract surgery.
The microscopy system may be a monoscopic microscopy system or a stereoscopic microscopy system. The stereoscopic microscopy system may have a left and a right observation channel. By means of the left and the right observation channel, a stereoscopic image of the object region can be generated, which is arranged in the object plane. The stereoscopic image can have two stereoscopic partial images. Each of the stereoscopic partial images can be an image of the object region in an image plane. The lens can be penetrated by the left and right observation channel.
According to an embodiment, a plurality of different focal plane positions may be controllably adjustable by means of or caused by the driving of the variable optics for a main plane of an object-side beam exit of the variable optics. By means of or caused by the different focal plane positions, the measurement focus between the cornea and the retina of the eye is adjustable.
The variable optics may include a main plane of an object-side beam output and a main plane of a light-source-side beam input. The main levels can each be assigned a focal plane. The two principal planes may represent the optical effect by which the portion of the measuring beam incident on the variable optics is transformed into the portion of the measuring beam which is off the variable optics. The main planes of the variable optics and their respective focal length can together represent all the optically active surfaces of the variable optics, which are penetrated by the measuring beam. In other words, the optical effect of all optically active surfaces of the variable optics, which are penetrated by the measuring beam, in the context of the paraxial optics can be described by the two principal planes and their respective focal lengths.
The focal plane of a principal plane may be defined as a plane perpendicular to the optical axis which contains the focal point of this principal plane. The focal plane may be a real or a virtual focal plane. A virtual focal plane may be defined as a plane containing a virtual focal point.
A parallel radiation beam incident on the variable optics on the light source side can be converted by the variable optics into a radiation beam emerging from the variable optics such that the emergent radiation beam has a real or virtual focus in a focal plane of the main plane of the object-side beam exit. Accordingly, a light source side incident beam having a virtual or real focus in a focal plane of the main plane of the light source side beam input can be converted by the variable optics into a parallel beam, which fails the object side of the variable optics.
The focal plane position may be an axial position of the focal plane measured relative to the optical axis. The focal plane position may be measured relative to a fixed reference point. The main plane position may change without the focal plane position changing. This also makes it possible for the focal plane of the main plane to change without the focal plane position changing.
An axial position of a measuring focus of the measuring beam, measured relative to the beam axis of the measuring beam, may be dependent on the focal plane position for the main plane of the object-side beam output of the variable optics. This focal plane can be imaged by a part of the measuring beam optics and / or by optically active components of the eye in a plane in which the measuring focus, in particular the beam waist, is arranged. The optically active ingredients may include the cornea and / or the natural lens of the eye. By means of the controllable adjustment of the focal plane position of the main plane of the object-side beam exit of the variable optics or caused by the controllable adjustment of the focal plane position, the defocusing of the measuring beam at the object distance, in particular the distance of the real or virtual focus from the object distance, can be controllably adjustable, which represents the defocusing. Alternatively or additionally, the measuring focus can thereby be positionable at the object distance. In particular, the driving of the variable optics for selectively setting the first state of the second state, the setting (a), the setting (b) and / or different defocusing at the object distance may comprise the controllable adjustment of the focal plane position.
According to another embodiment, the optical system may be configured such that a focal length of a principal plane of an object-side beam output of the variable optics is controllably adjustable to different values. At each of the values of the focal length, a focal plane position of the principal plane may be equal or substantially equal. The variable optics can be configured as a variable beam expander.
In the case of an identical or essentially the same focal plane position of the main plane of the object-side beam exit, a smaller absolute value (ie, a smaller amount) of the focal length can cause the aperture angle of the measurement beam emerging from the object side to increase. This can result in the measuring beam having a larger numerical aperture at the measuring focus. The larger numerical aperture may in turn result in the diameter of the beam waist decreasing in the measurement focus. With a smaller diameter of the beam waist, it is possible to acquire OCT data with a higher lateral resolution. The lateral resolution may be the resolution in a plane perpendicular to the axis of the measuring beam.
According to a further embodiment, the variable optics may be controllably adjustable into a plurality of afocal or substantial afocal configurations. The afocal configurations may have different values of afocal beam expansion.
The afocal beam expansion may be related to an object-directed light path. In other words, the afocal beam broadening may be defined as a ratio of a diameter of a parallel beam (D) projecting from the variable optics on the object side to a diameter of a parallel beam (d) incident to the variable optics on the light source side. This means that the afocal beam expansion can be calculated to be D / d.
The optical system may be designed so that the afocal beam expansion is continuously and / or discretely adjustable over an adjustment range which has values which are less than 4 and greater than 4.5. Alternatively, the adjustment range may have values that are less than 3 and greater than 4.5. Alternatively, the adjustment range may have values that are less than 2.5 and greater than 4.5. Alternatively, the adjustment range may have values that are less than 2 and greater than 5. Alternatively, the adjustment range may have values that are less than 6 and greater than 7. Alternatively, the adjustment range may have values that are less than 5 and greater are as 8. Alternatively, the adjustment range may have values that are less than 4.5 and greater than 9.
[0091] The optical system may be configured such that, by means of or caused by the activation of the variable optics, a numerical aperture of the section of the measuring beam tapering to the measuring focus can be adjusted continuously and / or discretely over a setting range, which values are less than or equal to 0, 02 and has values greater than or equal to 0.03. Alternatively, the adjustment range may have values less than or equal to 0.01 and values greater than or equal to 0.04. Alternatively, the adjustment range may have values less than or equal to 0.005 and values greater than or equal to 0.08.
A ratio of a maximum value (anax) of the numerical aperture to a minimum value (amin) of the numerical aperture (that is, the value amax / amin) which can be set by means of or caused by activation of the variable optics can be greater than 1 , 5, be greater than 1.7 or greater than 1.8 or greater than 2 or greater than 4. The ratio may be less than 10 or less than 20 or less than 30.
According to a further embodiment, the optical system is configured or configurable such that the measuring beam is incident on the variable optics as a parallel or substantially parallel beam.
According to one embodiment, the variable optics comprises a first movable optical unit. The first movable optical unit may have a negative refractive power.
Each of the movable optical units of the variable optics may be configured to perform a movement along and / or obliquely to an optical axis of the variable optics. For example, the variable optics may comprise one or more Alvarez lenses. Alternatively or additionally, one or more of the movable optical units may be configured so as to be selectively insertable and removable in the measuring beam. The movable optical units may each be movable depending on control signals of a controller. Each of the movable optical units may be drive coupled to one or more actuators. The optical system may include a controller which is in signal communication with the actuators. Depending on control signals transmitted from the controller to the one or more actuators, the movable optical units may be movable.
Movement of the movable optical units may in particular occur (a) in the adjustment of the different focal plane positions of the principal plane of the object-side beam exit of the variable optics, (b) in the adjustment of the focal length of this principal plane and / or (c) in the case of Setting the variable optics in one of the afocal configurations. In this case, a plurality of movable optical units can perform a relative movement relative to each other.
Alternatively or additionally, the variable optics may have one or more optical units which have a controllably changeable form of a refractive or reflective surface and / or a controllably variable refractive index. An optical unit may, for example, be one or a combination of a lens, a cemented element and a mirror. For example, the variable optics may comprise one or more liquid lenses.
According to a further embodiment, the variable optics has a first and a second movable optical unit. The first and second movable optical units may be controllably movable relative to one another.
According to a further embodiment, the first movable optical unit has a negative refractive power and the second movable optical unit has a positive refractive power. The refractive power can be understood to mean a spherical refractive power.
[0100] According to a further embodiment, the measuring beam enters the variable optics in the object-directed light path through the second movable optical unit. In other words, the second movable optical unit has an optically effective entry surface through which the measurement beam enters the variable optics.
According to another embodiment, the first movable optical unit, as seen relative to an object-directed light path of the measuring beam, downstream of the second movable optical unit is arranged.
[0102] According to a further embodiment, the variable optics has a third optical unit. The third optical unit may be located downstream of a first movable optical unit as viewed relative to an object-directed light path of the measuring beam. The first movable optical unit may have a negative refractive power. Alternatively or additionally, the third optical unit may be arranged downstream of a second movable optical unit. The second movable optical unit may have a positive refractive power. Alternatively or additionally, the measuring beam can leave the variable optics through the third optical unit along the object-directed light path. Alternatively or additionally, the third optical unit may have a positive refractive power. Alternatively or additionally, a position of a focal plane of a main plane of a light source-side beam input of the third optical unit may be arranged within the variable optical system. The third optical unit can have an optically effective exit area through which the measuring beam leaves the variable optics in the object-directed light path.
The variable optics may include a fourth optical unit. The fourth optical unit may be disposed between the first movable optical unit and the third optical unit. The fourth optical unit may have a positive or negative refractive power. The fourth optical unit may be a field lens.
According to another embodiment, the second movable optical unit has two separate optical subunits. The separate subunits may each have a positive optical power. The subunits may be spaced from each other.
A subunit can be for example one or a combination of a lens, a cemented element or a mirror. The light source side optical subunit may be formed as a cemented member. The object-side optical subunit can be designed as a lens.
BRIEF DESCRIPTION OF THE DRAWINGS The foregoing and other advantageous features will become more apparent from the following detailed description of the exemplary embodiments with reference to the accompanying drawings. It is emphasized that not all possible embodiments necessarily achieve all or some of the advantages indicated herein.
Fig. 1 is a schematic view of an optical system according to an embodiment;
FIG. 2A illustrates the observation channels of the microscopy system in the area of the object plane in FIG
Examination of the front section by the microscope system shown in FIG. 1;
FIG. 2B illustrates how the measuring focus of the OCT beam can be selectively positioned at the object plane or on the retina of the eye by means of the control of the variable optics, which are shown in FIG. 1;
Fig. 3 illustrates the measurement focus of the OCT system of the optical system shown in Fig. 1;
Figs. 4A and 4B illustrate how, by changing a focal plane constant focal position for an object-side major plane of the variable optics shown in Fig. 1, the numerical aperture of the OCT measurement beam is adjustable at the measurement focus;
Figures 4C and 4D illustrate different configurations of the variable optics of the OCT system shown in Figure 1, with which different values of afocal beam expansion are generated;
Fig. 5 illustrates the structure of the variable optics of the OCT system shown in Fig. 1;
Figures 6A and 6B illustrate different afocal configurations of the variable optics of the OCT system shown in Figure 1, with which different values of the numerical aperture in the object plane can be generated;
FIGS. 7A to 7C illustrate different configurations of the variable optics of the OCT system shown in FIG. 1, with which different defocusing of the OCT measurement beam in the object plane can be produced;
Fig. 8 illustrates the structure of the collector optics shown in Fig. 1;
FIGS. 9A to 9C illustrate various settings of the collector optics shown in FIG. 8, with which different diameters of the emergent parallel measuring beam can be generated;
Figs. 10A and 10B illustrate the measurement of anatomical parameters of the eye in the state of central fixation with the optical system shown in Fig. 1; and
Figures 11A and 11B illustrate the verification of the state of central fixation in response to OCT data acquired by the retina.
DESCRIPTION OF EXEMPLARY EMBODIMENTS FIG. 1 is a schematic representation of an optical system 1 according to an exemplary embodiment. The optical system 1 comprises an OCT system 2 and a microscopy system 3. The microscopy system 3 is designed as a stereoscopic microscope. However, it is also conceivable that the microscopy system 3 is designed as a monoscopic microscope. The microscopy system 3 is configured to generate two observation channels 19-1, 19-2 whose axes intersect in the object plane 40 at a stereo angle β. Each of the stereoscopic observation channels 19-1, 19-2 generates in an image plane 41-1, 41-2 of the respective observation channel 19-1, 19-2 a stereoscopic partial image of the object region, which is arranged in the object plane 40 of the microscopy system 3.
A beam of the first or the second observation channel 19-1, 19-2, which emanates from a point in the object plane 40, is converted by a lens 29 of the microscope system 3 in a beam which is parallel or substantially parallel. The microscopy system 3 further has a variable optical system 50 which is arranged in the beam path of the observation channels 19-1, 19-2 downstream of the objective 29. The variable optics 50 has two zoom components 50-1, 50-2, which are respectively penetrated by the beams of one of the observation channels 19-1, 19-2. Each of the two zoom components 50-1, 50-2 may be formed as an afocal optical system.
For each of the observation channels 19-1, 19-2, the microscopy system 3 each has a focusing optics 53-1, 53-2. For each of the observation channels 19-1, 19-2, the focusing optics 53-1, 53-2 are configured to focus beams of the respective observation channel 19-1, 19-2 emitted from one point in the object plane 40 onto one
Point in the image plane 41-1,41-2 to focus. The image planes 41-1, 41-2 are therefore optically conjugate to the object plane 40.
The microscope system 3 further includes an eyepiece 52-1, 52-2 for each of the observation channels 19-1, 19-2. Through the eyepieces 52-1, 52-2 through an observer the partial images generated in the image planes 41-1, 41-2 with the eyes 54-1, 54-2 are observable. Additionally or alternatively, it is conceivable that the optical system 1 has one or more image sensors (not shown in FIG. 1). The image sensor may be arranged in one of the image planes 41-1, 41-2 or in a plane which is optically conjugate thereto. The image sensor may be configured to capture one of the generated sub-images.
The OCT system 2 has an interferometer which generates a measuring arm and a reference arm. Through the interferometer, light which has passed through the measuring arm is brought into interference with light which has passed through the reference arm.
The OCT system 2 generates a measuring beam 9, which is guided along the measuring arm in an object-directed light direction to the eye 7. Scattered light of the measuring beam 9 is returned along the measuring arm in a reverse direction, which is reversed relative to the object-directed light direction. The returned light is made to interfere with the light which has passed through the reference arm.
A measuring beam optics of the OCT system 2 forms the measuring beam 9 such that the measuring beam forms a measuring focus 43 in the eye 7. In an OCT unit 21, the light of the measuring beam 9 is generated and transported via a light guide 23 to the measuring beam optics. Through a light exit surface 25, which is located at one end of the light guide 23, the light of the measuring beam 9 is emitted into the measuring beam optics. The light exit surface 25 thus forms a light entry into the measuring beam optics. The measuring beam optics is an imaging optic which is configured such that the portion of the measuring beam 9 incident on the eye 7 is adjustable as a parallel beam, a substantially parallel beam, a convergent beam, and / or a divergent beam. Thereby, the measurement focus 43 of the measurement beam can be generated at a selected location in the interior of the eye 7 in order to acquire OCT data from a selected location of the inside of the eye. The measuring focus is a picture of the light entry.
In particular, it is thereby possible that the measurement focus can be positioned in a central region between the cornea and the retina. By adjusting the axial measurement range to extend from the cornea to the retina, OCT data can then be acquired. Depending on these OCT data, the axial length of the eye to be examined can be determined.
Alternatively, the axial length of the eye may be determined by first acquiring OCT data from the anterior portion of the eye. Then, caused by the control of the variable optics, the measuring focus shifted from the front section to the retina. Thereafter, OCT data is collected from the retina. Depending on the OCT data of the anterior segment, the OCT data of the retina, and further depending on the distance over which the measurement focus has been shifted, then the axial length of the eye can be determined.
The precise measurement of the axial length of the eye using a Fundusabbildungssystems or a contact glass, however, is difficult only possible because the path difference between the reference and arm, which results from the additional inserted optical elements, must be considered. In addition, optical errors of these elements can lead to higher measurement inaccuracies.
The anterior chamber depth is another parameter that can be measured with the help of the OCT system with high accuracy, and whose determination is often used to determine the intraocular lens. This parameter can also be measured with high precision due to the axial displaceability of the measuring focus. The positionability of the measurement focus 43 on the retina 77 of the eye 7 further allows measurement light scattered at the retina 77 to be used for aberro-metric measurements. For this purpose, the optical system may have an aberrometric measuring system (not shown in FIG. 1).
The measuring beam optics has a collector optics 22, a scanning system 30, a variable optics 10, a deflection element 33 and the objective 29. The collector optic 22 is configured or controllably configurable such that a portion 10 of the measurement beam that fails from the collector optics 22 is parallel or substantially parallel. The collector optics 22 may be designed as a collimator lens. Alternatively, the collector optics 22 may be implemented as variable optics, wherein a convergence or divergence of a portion of the measurement beam 9, which precipitates from the collector optics 22, is adjustable. Alternatively or additionally, the collector optics 22 may be configured so that a diameter of a parallel or substantially parallel portion of the measuring beam 9, which precipitates from the collector optics 22 is controllably adjustable by the collector optics 22, so that before and after the change of the diameter of the portion of the Measuring beam 9 is parallel or substantially parallel. The structure of the collector optics 22 will be explained with reference to FIGS. 8 and 9.
The scanning system 30 is configured to scan the measurement focus 43 two-dimensionally laterally. As a result, the measuring focus 43 is moved in a scanning plane 42. The scanning system 30 has two scanning mirrors 31, 32, which are each mounted pivotably. The mirrors can be drive-connected with a piezo drive and / or a galvanometer drive.
FIG. 2A illustrates in detail for the optical system 1 shown in FIG. 1 the progress of the observation channels 19-1 and 19-2 of the microscopy system on the eye 7. The object plane 40 of the microscope is on the anterior surface of the cornea 76 arranged. The object plane 40 corresponds to the front focal plane of the objective 29 (shown in FIG. 1). The front focal plane of the objective 29 is that focal plane which is located on the side which faces the object. The beams of the observation channels 19-1 and 19-2 start from the object plane 40, so that the axes of the observation channels 19-1 and 19-2 form a stereo angle β.
As described in detail with reference to the following figures, the OCT system is configured such that, caused by a drive of the variable optics 10 (shown in FIG. 1), the axial position of the measuring focus of the measuring beam, measured relative to the axis of the measuring beam, and the beam waist diameter of the measuring focus controllably changeable. It has been shown that this is very beneficial. First, this can be done regardless of the position of the object plane of the microscopy system, an adjustment of the axial position of the measuring focus and the beam waist diameter. This allows the OCT system to be adapted for examination of a particular area of the eye, with the object plane remaining in the anterior portion of the eye. In particular, this allows the measurement focus to be selectively positioned in the anterior segment of the eye or on the retina of the eye. This allows efficient examination of different areas of the eye, with the anterior portion of the eye being able to remain under constant observation by the physician. It has been shown that this can be very advantageous, in particular in the performance of cataract surgery.
In particular, it has been found that anatomical parameters of the eye measured during cataract surgery, after the natural lens has been removed and before the intraocular lens is inserted, can be used to determine the effect of the intraocular lens to be used with high reliability ,
Furthermore, the optical system allows to dispense with the use of contact glasses and fundus imaging systems, thereby avoiding the disadvantages associated with the use of such systems.
The adjustment of the axial position of the measurement focus will be explained with reference to FIG. 2B. Caused by a control of the variable optics, the OCT system can be brought into a first and a second state. In FIG. 2B, the measuring beam in the first state is identified by the reference numeral 9-1 and the measuring focus in the first state is identified by the reference numeral 43-1. In the first state, the measurement focus 43-1 is arranged in the object plane 40. The measurement focus 43-1 is then in the front focal plane of the objective 29 (shown in FIG. 1). The scanning plane 42-1 of the measuring focus 43-1 is located in the object plane 40. To this end, the variable optics must be configured such that the measuring beam is incident on the objective as a parallel or essentially parallel beam. Since the portion 66 (shown in Fig. 1) of the measuring beam 9 incident on the variable optics is configured as a parallel beam, the variable optic in the first state must be configured as a confocal system. For example, in this first state, it is possible to take OCT measurements from a portion of the area imaged by the microscopy system. By way of example, OCT data representing a cross section of a region of the cornea can thereby be detected.
In FIG. 2B, the measuring beam in the second state is identified by the reference numeral 9-2 and the measuring focus in the second state is indicated by the reference numeral 43-2. In the second state, the measuring beam 9-2 has a defocusing in the object plane 40. The defocusing corresponds to a distance of a virtual or real focus from the object plane 40. The distance of the virtual or real focus is measured as a distance through air, that is, without the presence of the eye. In the second state, which is illustrated in FIG. 2B, this distance is infinite, that is, the measuring beam 9-2 arrives at the object plane 40 as a parallel beam. If the eye 7 is correct and not accommodated, the measuring beam 9-2 is focused on the retina 77 of the eye 7. This makes it possible to acquire OCT data from areas of the retina 77. In this case, the object plane 40 remains on the cornea 76. The front region of the eye 7 can therefore remain in the acquisition of OCT data from the retina 77 under constant further observation by the microscopy system.
For the second state shown in FIG. 2B, since the measuring beam is incident on the variable optics as a parallel beam, the focal plane 15 (shown in FIG. 1) of the main plane of the object-side beam exit of the variable optics 10 must be in the rear Focal plane of the lens 29 are located. As a result, the measuring beam 9 is incident parallel to the object plane 40. The rear focal plane is the focal plane of the objective 29, which is located on the side which faces away from the eye 7.
If the eye 7 is ill-looking or not accommodated, then the measurement beam in the object plane 40 must have a defocus, which corresponds to a finite distance of the real or virtual focus from the object plane 40. For example, if the eye has an ametropia of +5 D or -5 D, the distance of the real or virtual focus from the object plane 40 must be 200 millimeters.
In order not only to allow a study of right-eye, but also eyes of different refractive errors, the OCT system is designed so that the OCT system is selectively adjustable between a parallel beam path in the object plane 40 and a defocusing in the object plane 40 wherein the defocus corresponds to a virtual or real focus distance from the object plane 40 that is less than 300 millimeters, less than 200 millimeters, or less than 180 millimeters, less than 150 millimeters, less than 130 millimeters or less is less than 80 millimeters or less than 80 millimeters or less than 70 millimeters. The greater the amount of ametropia of the eye to be examined, the lower must be the distance of the real or virtual focus from the object plane.
In order to obtain OCT data from the retina of the aphakic eye during cataract surgery, the OCT system is further configured to adjust the defocus so that the distance of the real or virtual focus from the objective is between 50 millimeters and 150 Millimeters is greater than the distance of the object plane from the lens. The virtual or real focus of the measuring beam is then on that side of the object plane which faces away from the objective. This defocusing makes it possible to arrange the measurement focus on the retina in an aphakic eye. It has been shown that by measuring the aphakic eye, the intraocular lens to be used can be measured with greater reliability.
The measuring focus 43 of the measuring beam 9 is shown in detail in FIG. 3. The axial position relative to the axis A of the measurement beam 9, at which the measurement focus 43 has a narrowest constriction, is defined as a beam waist 13. At the beam waist 13, the measuring beam 9 has a beam waist diameter W. By the lateral scanning of the measuring focus 43, the beam waist 13 is moved in the scanning plane 42. The laser beam has an opening angle α in the far field, with which the measuring beam 9 approaches the measuring focus 43. The opening angle α in the far field is a measure of the numerical aperture of the measuring beam at the measuring focus. The measuring focus 43, in particular the beam waist 13, is located within an axial measuring range B of the OCT system, via which the scattering intensities are detected by the OCT system.
As already discussed with reference to FIG. 2A, the variable optic is configured such that an axial position of the measuring focus 43 is controllably adjustable along the axis A of the measuring beam 9. This makes it possible to arrange the measuring focus 43 within the inside of the eye to a desired position.
The measuring beam optic is further configured such that for the first and the second state (shown in FIG. 2B), the opening angle α of the measuring beam 9 is controllably adjustable. The beam waist diameter W is dependent on the opening angle α in the far field. This makes it possible that for selected measuring positions in the eye interior, the lateral resolution of the OCT system in the beam waist is adjustable. As can be seen in FIG. 2B, in the second state the diameter d of the parallel or substantially parallel measuring beam 9-2 incident on the object plane 40 must be varied for this purpose. The adjustment of the opening angle, or the beam diameter, is explained in more detail with reference to FIGS. 4A and 4B.
It has been found that this is particularly advantageous, since it is thereby possible to measure extended structures in the interior of the eye effectively with the aid of the OCT system. In particular, this makes it possible for α OCT data of a comparatively large area within the interior of the eye to be detectable initially with a small opening angle. A small opening angle α in the far field reduces the lateral resolution in the beam waist, but allows the use of a large axial measuring range, since the increase of the beam diameter with increasing distance from the beam waist 13 by the small opening angle α is smaller.
From the OCT data of the detected large area, a target area can then be determined, from which then OCT data with a low axial waist area W (that is, with a low beam waist diameter W, ie with a high lateral resolution in the beam waist 13 in Fig. 3) are detected. The optical system according to the embodiment shown makes it possible to change the lateral resolution in the beam waist without moving the beam waist 13 along the axis A of the measuring beam 9.
The structure and operation of the variable optics 10 will be explained in detail with reference to FIGS. 4A to 7C.
The variable optic 10 is configured such that a plurality of different focal plane positions are controllably adjustable for a main plane of an object-side beam output of the variable optics. The focal plane positions are measured relative to a fixed reference point.
As shown in FIG. 4A, at least in some of the variable optics configurations, the focal plane may be a virtual focal plane FP. In the variable optics configuration 10 shown in FIG. 4A, a parallel incoming beam 60 produces a divergent outgoing beam 61. The outgoing beam 61 is therefore not focused in a real focus, but shines from a virtual divergence point DP which is arranged in the virtual focal plane FP of the main plane of the object-side beam exit. The focal plane FP is determined assuming a parallel incident beam 60 incident on the variable optic 10.
The portion of the measuring beam 66 (shown in FIG. 1) incident on the variable optics 10 may be configured as a convergent divergent beam, a parallel or substantially parallel beam. Therefore, the point of divergence of the outgoing portion of the measuring beam 67, which fails from the variable optics 10, does not necessarily have to coincide with the virtual divergence point DP (shown in FIG. 4A), which results under the assumption of the parallel incident beam 60.
Further, as illustrated by the comparison of FIGS. 4A and 4B, the variable optic 10 is configured such that for at least one of the plurality of focal plane positions, the associated focal length is controllably adjustable to different values, with the focal plane position the focal plane FP remains the same or substantially the same. In each of FIGS. 4A and 4B, the variable optic 10 is configured such that the focal plane FP has a same position measured relative to a fixed reference point. However, the associated focal lengths ίΊ and f2 are different.
In the configuration of Fig. 4B, the main plane PP2 of the object-side beam output is closer to the focal plane FP as compared with the configuration of Fig. 4A. The displacement of the main plane is effected by a movement of movable optical units 11 and 12, which will be described in more detail below with reference to FIG. Since the focal length is calculated from the distance between the principal plane and the focal plane FP, the absolute value of the focal length T of the configuration of FIG. 4A is larger than the absolute value of the focal length f2 of the configuration of FIG. 4B.
The reduced absolute value of the focal length of the configuration of FIG. 4B compared to the configuration of FIG. 4A results in that the outgoing beam 61 generated by the parallel incident beam 60 in the configuration of FIG. 4B a larger opening angle θ2, compared with the opening angle θι the configuration of Fig. 4A. However, in both configurations, the outgoing beam 61 is such that it appears to come from a divergence point DP with the same position, which is arranged in the focal plane of the object-side main plane.
This has the consequence for the measuring beam that the opening angle α in the far field (shown in FIG. 3) of the measuring beam 9 converging on the measuring focus 43 changes, but the axial measuring focus position remains the same. In the case of a fixed focal plane position of the focal plane FP, the different settings of the focal length can thus cause the lateral resolution in the scan plane 42 to change without the scan plane 42 being displaced in its axial position relative to the axis A of the measurement beam 9. This allows the surgeon to easily and quickly change between overview and detail shots during surgery.
The OCT system is further configured such that the variable optics are controllably adjustable in a plurality of afocal or substantially afocal configurations having different values of afocal beam expansion. This will be described below with reference to Figs. 4C and 4D.
An afocal system forms a parallel outgoing beam 61 from an incident parallel beam 60. The focal planes of an afocal system therefore lie at infinity. The afocal beam expansion can be defined relative to the object-directed light path. In particular, the beam expansion can be defined as the ratio of the diameter of the object side parallel beam to the diameter of the light source side parallel beam.
FIGS. 4C and 4D each show an afocal configuration in which the variable optic 10 is controllably adjustable. In the second configuration shown in FIG. 4D, the variable optic 10 is configured such that the ratio between the diameter D2 of the emergent beam and the diameter of the incident beam d2 (ie, the size D2 / d2) is greater than the ratio between the diameter D1 of the outgoing beam and the diameter d-ι of the incident beam of the first configuration (ie the size Di / di), which is shown in Fig. 4C. Therefore, the afocal beam expansion is larger in the second configuration than in the first configuration.
In particular, if the incident portion of the measurement beam 66 (shown in FIG. 1) incident on the variable optics 10 is configured as a parallel light beam, the larger confocal beam expansion results in the measurement beam having a larger aperture angle α in the far field (shown in Fig. 3) to the measuring focus 43 tapers. The measuring beam then has a larger numerical aperture at the measuring focus. In the optical system, which is shown in FIG. 1, the measuring beam incident in parallel on the objective 29 is focused in the object plane 40 of the objective 29, which at the same time is the focal plane of the objective 29.
The variable confocal beam broadening can therefore be used to change the lateral resolution of the measurement beam 9 in the focal plane of the objective without displacing the beam waist 42 (shown in FIG. 3) along the axis of the measurement beam 9.
Fig. 5 is a schematic view of the measuring beam optics of the optical system 1, which is shown in Fig. 1. To simplify the illustration, the measuring beam 9 is shown in FIG. 5 with a straight-line beam axis. The measuring beam 9 is emitted through a light exit surface 25, which is located at the end of an optical fiber 23, into the measuring beam optics 22. The portion of the measuring beam 9, which emerges from the light exit surface 25, impinges on a collector optics 22, which is configured as collimator optics. The measuring beam 9 emerges from the collector optics 22 as a parallel or substantially parallel beam. The portion of the measuring beam 9, which emerges from the collector optics 22, enters the scanning system 30, which has the scanning mirrors 31 and 32, which are only shown roughly schematically in FIG.
The portion of the measuring beam 9 emerging from the scanning system 30 strikes a second movable optical unit 11. A movable optical unit may be defined as having one or more optically effective areas, all the optically effective areas of the unit being a unit are movable while maintaining their arrangement relative to each other. In other words, in the movement of the movable optical unit, the optically effective surfaces do not move relative to each other. The second movable optical unit 11 has the optically effective areas S1 to S5. The second movable optical unit 11 has first and second optical sub-units 26, 27 each having a positive optical power and spaced from each other. The first optical subunit 26 is formed as a cemented member, the second optical subunit 27 is formed as a lens.
The section of the measuring beam 9 emerging from the second movable optical unit 11 strikes a first movable optical unit 12. The first movable optical unit 12 is designed as a biconvex lens and has the optically active surfaces S6 and S7.
The second movable optical unit 11 has a positive optical power. The first movable optical unit 12 has a negative optical power. In the afocal configuration of the variable optics 10 shown in FIG. 5, the portion of the measuring beam 14 exiting the first movable optical unit 12 forms a real focus 14. The real focus 14 is located between the first movable one optical unit 12 and the third optical unit 13. The portion of the measuring beam 9 diverging from the real focus 14 strikes the third optical unit 13. The third optical unit 13 has the optically effective surfaces S8 to S10. The third optical unit 13 is a stationary optical unit. However, it is also conceivable that the third optical unit 13 is a movable optical unit. The portion of the measuring beam emerging from the third optical unit 13 impinges on the deflecting element 33, which is also shown only roughly schematically in FIG. The section of the measuring beam which emerges from the deflecting element 33 impinges on the objective 29. The objective 29 has the optically effective surfaces S11 to S13. In particular, in the afocal configurations of the variable optics 10, the focal length of the third optical unit 13 is greater than or greater than 1.5 times, or greater than two times, or greater than three times the focal length of the optical component consisting of the first and the second movable optical unit 12, 11 is formed.
FIGS. 6A to 7C each show part of the measuring beam optics, the variable optics 10 being shown in different configurations in which the variable optics are controllably adjustable. In FIGS. 6A and 6B, the variable optics 10 are shown in configurations in which the measurement focus 43 (shown in FIG. 3) of the measurement beam 9 is focused onto the object plane 40 of the microscopy system. The beam waist 13 (shown in FIG. 3) is then in the object plane 40. For each of the observation channels 19-1 and 19-2 (shown in FIG. 1) of the microscopy system, the beam path downstream of the objective 29 is parallel or parallel Essentially parallel. Therefore, also the portion of the measuring beam 9, which is incident on the objective 29, must be parallel or substantially parallel so that the beam waist of the measuring beam 9 is arranged in the object plane 40.
In the configurations shown in FIGS. 6A and 6B, variable optics 10 are each configured as an afocal system, which includes a parallel or substantially parallel incident portion 66 of the measurement beam into a parallel or substantially parallel emergent portion 67 of the measuring beam transforms. The precipitating portion 67 has a larger diameter than the incident portion 66. As a result, an enlargement of the numerical aperture of the portion of the measuring beam 9 is effected, which tapers to the object plane 40. The failing portion 67 of the measuring beam 9 impinges on the objective 29 and is focused in the focal plane of the objective, which is simultaneously the object plane 40 of the microscope system.
In both afocal variable optics configurations, a first optical component consisting of the first and second movable optical units 11, 12 generates from the incident portion 66 of the measuring beam 9 a real focus 14 within the variable optics. Therefore, a focal plane position of a principal plane of the object-side beam output of this first optical component is arranged within the variable optics. Further, this focal plane of the first optical component is arranged in a focal plane of a main plane of a light source side beam input of a second optical component consisting of the third optical unit 13. This focal plane of the second optical component has a distance f3 from the main plane of the light source side beam input of the third optical unit 13 in both configurations.
In the configuration of FIG. 6B, the variable optic 10 has less beam expansion compared to the configuration of FIG. 6A. Consequently, the opening angle a2 of the measuring beam, with which the measuring beam 9 tapers to the object plane 40, is less than the corresponding opening angle α-ι in the configuration of FIG. 6A. The aperture angles .alpha.-1 and a2 relate to the far field of the measuring beam 9. The numerical aperture of the section of the measuring beam which tapers towards the measuring focus is determined as a function of the aperture angle .alpha.-1 or a2. For the configuration of FIG. 6A, this results in a numerical aperture of 0.04 and for the configuration of FIG. 6B, this results in a numerical aperture of 0.02. Therefore, by the configuration of Fig. 6A, a higher lateral resolution in the beam waist can be obtained as compared with the configuration of Fig. 6B. However, with the configuration of FIG. 6B, because of the small numerical aperture, OCT scans with a high scanning depth can be performed since the increase of the beam diameter is smaller with increasing distance from the beam waist due to the small aperture angle a2 compared to the configuration of FIG 6A.
FIGS. 7A to 7C show configurations with which the measurement focus of the measurement beam 9 is generated in the retina of the eye. In the configuration of FIG. 7A, the variable optic 10 is configured so that the section 66 of the measuring beam incident on the variable optics 10, which is parallel or substantially parallel, produces a portion of the measuring beam 68 which fails the objective 29; wherein this precipitating portion 68 is parallel or substantially parallel. The variable optics 10 and the lens 29 together thereby form an afocal or a substantially afocal system. The light entry into the measuring beam optics is therefore determined by the measuring beam optics to infinity or
Essentially imaged to infinity. The measuring beam 9 therefore falls on the object plane 40 as a parallel or essentially parallel beam and generates a measuring focus on the retina in the case of a right-aligned, unaccommodated eye.
In the configuration of FIG. 7B, a parallel or substantially parallel configured section 66 of the measurement beam incident on the variable optics 10 causes the measurement beam 9 to arrive on the object plane 40 as a divergent beam. In the configuration shown in FIG. 7B, a real focus 16 is generated in the area between the objective 29 and the object plane 40. The real focus 16 is a divergence point from which the measurement beam 9 freely propagates to the object plane 40. As a result, the measuring beam in the object plane 40 has a defocusing, which corresponds to a focal distance s-1 between the real focus 16 and the object plane 40.
In the configuration shown in Fig. 7B, the focal distance Si has a length of 200 millimeters. Therefore, the divergence of the measuring beam 9 in the object plane 40 is such that the measuring beam is focused on the retina in the case of an unaccommodated, refractive eye with a defective vision of -5 dpt. In order to enable a focus on the retina in eyes, which have a refractive error in a range between 0 dpt and -5 dpt, the variable optics is so controllable configurable that the measuring beam 9 in the object plane 40 has a lower divergence, that is , a corresponding distance of a real or virtual focus from the object plane 40 is greater than the distance si of the configuration of FIG. 7B. For this purpose, a real focus of the measuring beam, as seen relative to the object-directed light path, can also be located in the objective 29 or upstream of the objective 29. In this case, the measuring beam 9 no longer propagates freely between the real focus and the object plane 40. Consequently, the distance between the real focus and the object plane 40 is no longer identical to the distance of the corresponding virtual focus, which represents the defocusing in the object plane. In other words, the defocusing in the object plane 40 then corresponds to a spaced-apart virtual focal point. At an incident portion 66 of the measuring beam 9 configured as a parallel beam, this virtual focal point corresponds to the virtual focal point of the principal plane of the object-side beam output of an optical system formed of the variable optics 10 and the objective 29.
In the configuration of FIG. 7C, the measuring beam 9 converges convergently on the object plane 40. The measuring beam 9 is configured such that the measuring focus is on the retina in the case of an unaccommodated, sighted eye with a spherical refractive error of +6 dpt. Without the presence of the eye 7, the convergent measuring beam generates on the side of the object plane 40, which faces away from the objective 29, a focus which has a focal distance s 2 from the object plane 40. According to the ametropia of +6 D, this focus distance has a length of 160 mm. The focal distance S2 is indicated only schematically by the dashed arrow shown in FIG. 7C. Therefore, the defocusing of the measuring beam in FIG. 7C corresponds to a distance of a real focus from the object plane 40 of the size s2.
In order to enable a focus on the retina in eyes, which have a refractive error in a range between 0 dpt and +6 dpt, the variable optics is controllably configurable so that the measuring beam 9 in the object plane 40 has a lower convergence , that is, a corresponding focal distance s2 is greater.
The optically effective areas of the configurations shown in Figs. 6A to 7C have the radii of curvature and distances shown in Table 1. As explained with reference to FIG. 5, the second movable optical unit 11 has the optically effective areas S1 to S5. The first movable optical unit has the optically effective areas S6 and S7. The third optical unit has the optically active surfaces S8 to S10. The objective has the optically effective surfaces S11 to S13.
The diameters of the optically active surfaces, the materials of the optical elements and the refractive index which these materials have at a wavelength of the measuring beam of 1060 nanometers are shown in Table 2.
In the configuration of Fig. 7B, the first optical component consisting of the first movable optical unit 11 and the second movable optical unit 12 generates neither a real focus nor a virtual focus within the variable optics. In the configuration of FIG. 7B, the variable optic is configured such that the focal plane position of the main plane of the object-side beam output of the first optical component is located outside the variable optics. On the other hand, in the configurations of Figs. 7A, 6A, 6B, 7A and 7C, this focal plane is located within the variable optics.
This large displaceability of the focal plane position makes it possible to adapt the defocusing of the measuring beam 9 in the object plane 40 to a large range of refractive errors of the eye. In particular, this makes it possible to generate the divergent measuring beam shown in FIG. 7B in the object plane 40, which allows an examination of eyes having a defective vision of -5 dpt.
FIG. 8 illustrates the structure of the collector optics 22 for the OCT system of the optical system 1 shown in FIG. 1. The collector optics 22 has a variable focal length. The focal length of the collector optics 22 can be controllably changed such that, for different values of the focal length, the section 69 of the measuring beam 9, which precipitates from the collector optics 22, is parallel. For the different values of the focal length, a diameter of the
Section 69 each different. Therefore, the different values of the focal length of the collector optics cause different values of the numerical aperture of the portion of the measuring beam 9 tapering towards the measuring focus 43.
This embodiment of the collector optics 22 makes it possible to optimize the variable optics for the function of adjusting the axial measuring focus position, since the variable optics no longer have to take over the function of setting the numerical aperture. The displacement of the measuring focus along the axis of the measuring beam is then effected by the control of the variable optics, however, causes the setting of the numerical aperture of the measuring beam at the measuring focus by the control of the collector optics. By dividing these two functions into two separate optical systems, extended ranges for adjusting the axial measurement focus position and / or the numerical aperture can be obtained. Furthermore, this makes it possible to build the variable optics more compact, whereby a space saving in the surrounding area of the lens is effected. Furthermore, this is achieved in that the measuring beam 9 is guided as a parallel beam through the scanning system 30, rather than as a convergent or divergent beam. This prevents the image quality of the OCT data from being affected by Doppler effects if the scan mirrors are not perfectly aligned relative to each other. Further, it is avoided that the relationship between the scanning position and the rotation angle of the mirrors is different for the scanning mirrors.
FIG. 8 shows the structure of the collector optics 22. The collector optics 22 form a section of the measuring beam which emerges from the light exit surface 25 of the optical fiber 23 into a section 69 of the measuring beam 9, which precipitates from the collector optics 22 and which is parallel for different values of an adjustable focal length of the collector optics 22.
As shown in FIG. 8, the collector optics 22 includes a first movable optical unit 72 and a second movable optical unit 73. The first movable optical unit 72 has a negative refractive power. The second movable optical unit 73 has a positive refractive power. The second movable optical unit 73 is disposed downstream of the first movable unit 72 as seen in the object-directed light path of the measuring beam 9. Due to the second movable unit 73, the measuring beam 9 leaves the collector optics 22. For different values of the adjustable focal length of the collector optics 22, the section 69 of the emergent measuring beam 9 is in each case parallel.
The collector optics 22 has a third optical unit 71, which is arranged upstream of the first movable unit 72. The third optical unit 71 has a positive refractive power. Furthermore, the collector optics 22 has a fourth optical unit 70. The fourth optical unit 70 is disposed upstream of the third optical unit 71 and also has a positive refractive power. Through the fourth optical unit 70, the measuring beam 9 enters the collector optics 22. A portion 75 of the measuring beam 9, which fails from the fourth optical unit 70, is parallel. Between the fourth optical unit 70 and the third optical unit 71, a diaphragm 74 is arranged.
Collector optics 22 are configured such that, for different values of the focal length of the collector optics, a diameter of section 69 of measuring beam 9, which precipitates from collector optics 22, is controllably adjustable to different values. For the different values of the diameter, the portion 69 of the measuring beam 9, which fails from the collector optics 22, is parallel. As a result, different values of the numerical aperture can be set at the measuring focus,
wherein, for each of the different values, the measuring beam 9 passes as a parallel beam through the scanning device 30 (shown in Fig. 1).
The optically active surfaces of the collector optics 22, which are shown in FIG. 8, have the radii of curvature, distances and diameters shown in Table 3. Furthermore, Table 3 shows the materials of the optical elements and the refractive indices which comprise these optical elements at a wavelength of the measuring beam of 1060 nanometers. The first movable optical unit 72 has the optically effective surfaces S20 and S21. The second movable optical unit 73 has the optically effective areas S22 and S23. The third optical unit 71 has the optically active surfaces S18 and S19. The fourth optical unit 70 has the optically active surfaces S15, S16 and S17. The fourth optical unit 70 may be implemented as a cemented member.
Figures 9A to 9C show three configurations of the collector optics 22 to produce different diameters of the parallel outgoing portion 69 of the measuring beam. The configuration of the collector optic 22 shown in FIG. 9A produces a diameter ρΊ of 0.36 millimeter. The configuration of the collector optic 22 shown in FIG. 9B produces a diameter p2 having a value of 0.72 millimeters. The configuration of collector optics 22 shown in Figure 9C produces a diameter p3 of 1.44 millimeters.
As shown in Fig. 1, the optical system 1 has a fixing light device 87 for generating a real or virtual fixation point for the eye. The real or virtual fixation point can be seen by the patient with the eye 7 to be examined, in particular when the eye is positioned so that the cornea is located in the object plane 40. By looking at the fixation point, a central fixation of the fixation point by the eye 7 takes place. In the central fixation, the image of the fixation point is located in the foveolar center of the eye 7. Micro-movements of the eye are neglected here. The foveola is the area of the sharpest vision within the fovea. The diameter of the foveola is about 0.33 millimeters.
The fixation point may be defined by a real or virtual image generated by the fixation light device 87. The real or virtual image may be, for example, a crosshair or a circle. The fixation point may then be, for example, the center of the reticle or the center of the circle.
The fixing light device 87 comprises a fixing light unit 80. The fixing light unit 80 has a fixing light source which generates a fixing light 81, which is directed by a deflection element 82 onto the objective 29. The fixing light 81 passes through the objective 29. It is conceivable that the fixing light also passes through the variable optics 10. The fixing light source may comprise, for example, an LED and / or a laser. The fixing light 81 may have a light wavelength of the visible spectrum, by which the patient's fixing light 81 is well distinguishable from the illumination light of an object plane illumination (not shown in FIG. 1) of the optical system 1. For example, this wavelength of light may be in the green spectral range. Alternatively or additionally, the optical system 1 may be configured such that the intensity of the fixing light 81 changes according to a temporal pattern. For example, the intensity of the fixing light 81 may increase and decrease in time periodically, and / or the fixing light 81 may be triggered in time. A time-triggered fixation light may be, for example, a blinking fixation light.
The real or virtual fixing point, which is generated by the fixing light device 87, has a large distance from the object plane 40. Therefore, with central fixation of the fixation point, an alignment of the visual axis of the eye 7 takes place along a defined visual axis direction, essentially independently of the position of the eye in a direction perpendicular to the visual axis direction.
In the optical system 1 shown in FIG. 1, the fixing light 81 is configured so that this defined visual axis direction is parallel to the optical axis OA of the objective 29. Further, the OCT system 2 is configured such that the axis of the measuring beam 9 extends along the optical axis OA of the objective 29.
This allows a precise measurement of the anterior chamber depth, the lens thickness and the axial length of the eye. This will be explained below with reference to Figs. 10A and 10B.
Fig. 10A shows the eye 7 in a state in which the fixation point is centrally fixed. The fixation visual axis of the eye, that is to say the visual axis of the eye in the state of the central fixation, is identified by the reference symbol FA. In this state, the image 79 of the fixation point is located in the foveola center 78. The fixation visual axis FA is defined as the connection line between the foveola center 78 and the fixation point when the eye is in the state of central fixation.
The eye is positioned relative to the optical system such that when the scan system is scanned, an axis of the incident portion of the measurement beam 9 is along or substantially along the fixation visual axis FA. This makes it possible to determine a plurality of anatomical parameters with high precision by OCT measurements, such as the anterior chamber depth 82, the lens thickness 83, the distance 84 between the posterior lens capsule 85 and the retina 77, and the axial length 86 of the eye 7.
Fig. 10B, in comparison with Fig. 10A, illustrates the eye in a state in which the fixation point is not centrally fixed. The image 79 of the fixation point is then outside the foveolament center 78. As can be seen in FIG. 10B, the lengths 88a, 89a, 90a and 86a measured along the axis of the measurement beam 9 then deviate from those shown in FIG. 10A anatomical parameters of the anterior chamber depth 82, the lens thickness 83, the distance 84 between the posterior lens capsule 85 and the retina 77, and the axial length 86 of the eye 7.
As will be explained with reference to Figs. 11A and 11B, the optical system is designed so that the state of the central fixation is verifiable depending on OCT data detected by the retina.
FIG. 11A shows a first B-scan which represents a cross section through the upper layers 91, 92, 93, 94 of the retina. The OCT data of Fig. 11A was detected in the state shown in Fig. 10A, that is, in a state in which the fixation point is centrally fixed by the eye. The B-Scan can represent part of a volume scan. The cross section is configured to contain the image of the foveola center. Therefore, in the B-scan, the depression 95 of the fovea, which represents the foveola, can be recognized. The foveolament is located at a scanning position SP.
Fig. 11B shows a second B-scan at the same scan positions as in Fig. 11A. However, the OCT data of Fig. 11B was detected in the state of the eye which is shown in Fig. 11B, and in which the fixation point is not centrally fixed by the eye.
Therefore, in the OCT data shown in Fig. 11B, the foveolam center does not appear at the scanning position SP, as shown in the OCT data of Fig. 11A. Consequently, it can be checked on the basis of the OCT data whether the eye is in a state in which the fixation point is centrally fixed.
The optical system is configured to determine, depending on the OCT data, whether the image of the foveola center is at the scan position SP and / or whether a deviation of the image of the foveola center from the scan position SP is within a predetermined limit. This makes it possible to determine whether parameters detected by measurements on the eye are within a required accuracy. The OCT data may represent a two-dimensional scan or a volume scan.
The scan position SP can be determined, for example, by detecting OCT data from the retina over a longer period of time, at which the fixation light is activated. When the fixation light is activated, the eye is predominantly in a state of central fixation. If the eye is correct and not accommodated, the scanning position SP is that in which the axis of the portion of the measuring beam incident on the eye runs parallel to the fixation visual axis. In the system shown in FIG. 1, this is then the scanning position at which the measuring beam 9 runs along the optical axis.
Consequently, the optical system easily enables to check the state of the central fixation depending on OCT data detected by the retina.
In particular, thereby, the anatomical parameters shown in Fig. 10A can be reliably determined during a cataract operation.
When checking the state of the central fixation as a function of the OCT data, the measurement focus does not necessarily have to be in the area of the retina. It is conceivable to acquire OCT data from anatomical structures to be measured within the eye simultaneously with OCT data from the retina. Such an anatomical structure may for example be the natural lens. The measurement focus may be outside the retina, such as in the natural lens or in the area between the natural lens and the retina, but the axial range extends to the retina.
Depending on the OCT data, on the one hand, then, the anatomical structure can be measured and, on the other hand, it can be checked whether the eye is in the state of central fixation. The optical system according to the embodiment makes it possible to configure the axial position of the measuring focus and / or the numerical aperture at the measuring focus by controlling the variable optics and / or by controlling the collector optics.
Alternatively, in order to measure the eye length, it is also conceivable to acquire OCT data at different times so that the data represent different states of the eye.
If the number and the time interval of the different times are appropriately selected, the measured values then represent the axial length 86 (shown in FIG. 10A) in the state of the central fixation 86 and, on the other hand, measured values in states which deviate from the central fixation. such as the measured value 86a (shown in Fig. 10B). It has been shown that in the state of central fixation the measured values are maximum. If measured values are recorded over a longer period of time, the maximum values represent the axial length of the eye. To record comparison values in which the eye is not in the state of central fixation, the fixation light can be switched off.
1. An optical system (1) for examining an eye (7), the optical system (1) comprising: an OCT system (2) which is configured to generate a measuring beam (9) which is incident on the eye ( 7) impinges;

权利要求:
Claims (22)
[1]
from the anatomical parameters of anterior chamber depth 82, lens thickness 83, distance 84 between posterior lens capsule 85 and retina 77, and axial length 86 of eye 7, as shown in FIG 11A and 11B, the optical system is designed such that the state of the central fixation is verifiable depending on OCT data detected by the retina. FIG. 11A shows a first B-scan which represents a cross section through the upper layers 91, 92, 93, 94 of the retina. The OCT data of Fig. 11A was detected in the state shown in Fig. 10A, that is, in a state in which the fixation point is centrally fixed by the eye. The B-Scan can represent part of a volume scan. The cross section is configured to contain the image of the foveola center. Therefore, in the B-scan, the depression 95 of the fovea, which represents the foveola, can be recognized. The foveolament is located at a scanning position SP. Fig. 11B shows a second B-scan at the same scan positions as in Fig. 11A. However, the OCT data of Fig. 11B was detected in the state of the eye which is shown in Fig. 11B, and in which the fixation point is not centrally fixed by the eye. Therefore, in the OCT data shown in Fig. 11B, the foveolam center does not appear at the scanning position SP, as shown in the OCT data of Fig. 11A. Consequently, it can be checked on the basis of the OCT data whether the eye is in a state in which the fixation point is centrally fixed. The optical system is configured to determine, depending on the OCT data, whether the image of the foveola center is at the scan position SP and / or whether a deviation of the image of the foveola center from the scan position SP is within a predetermined limit. This makes it possible to determine whether parameters detected by measurements on the eye are within a required accuracy. The OCT data may represent a two-dimensional scan or a volume scan. The scan position SP can be determined, for example, by detecting OCT data from the retina over a longer period of time, at which the fixation light is activated. When the fixation light is activated, the eye is predominantly in a state of central fixation. If the eye is correct and not accommodated, the scanning position SP is that in which the axis of the portion of the measuring beam incident on the eye runs parallel to the fixation visual axis. In the system shown in FIG. 1, this is then the scanning position at which the measuring beam 9 runs along the optical axis. Consequently, the optical system easily enables to check the state of the central fixation depending on OCT data detected by the retina. In particular, thereby, the anatomical parameters shown in Fig. 10A can be reliably determined during a cataract operation. When checking the state of the central fixation as a function of the OCT data, the measurement focus does not necessarily have to be in the area of the retina. It is conceivable to acquire OCT data from anatomical structures to be measured within the eye simultaneously with OCT data from the retina. Such an anatomical structure may for example be the natural lens. The measurement focus may be outside the retina, such as in the natural lens or in the area between the natural lens and the retina, but the axial range extends to the retina. Depending on the OCT data, on the one hand, then, the anatomical structure can be measured and, on the other hand, it can be checked whether the eye is in the state of central fixation. The optical system according to the embodiment makes it possible to configure the axial position of the measuring focus and / or the numerical aperture at the measuring focus by controlling the variable optics and / or by controlling the collector optics. Alternatively, in order to measure the eye length, it is also conceivable to acquire OCT data at different times so that the data represent different states of the eye. If the number and the time interval of the different times are appropriately selected, the measured values then represent the axial length 86 (shown in FIG. 10A) in the state of the central fixation 86 and, on the other hand, measured values in states which deviate from the central fixation. such as the measured value 86a (shown in Fig. 10B). It has been shown that in the state of central fixation the measured values are maximum. If measured values are recorded over a longer period of time, the maximum values represent the axial length of the eye. To record comparison values in which the eye is not in the state of central fixation, the fixation light can be switched off. wherein the OCT system (2) comprises a lens (29) and a variable optics (10), wherein the variable optics (10), seen relative to an object-directed light path of the measuring beam (9), upstream of the lens (29) is arranged ; wherein the variable optic (10) comprises a first optical component having an optically active entrance surface through which the measuring beam (9), in the object directed light path, enters the variable optic (10) and wherein the first optical component further comprises a focal plane of a Main plane of an object-side beam output of the first optical component; wherein the variable optic (10) is controllably configurable into a first configuration in which a focal plane position of the first optical component is within the variable optic (10); and the variable optics is controllably configurable into a second configuration in which the position of the focal plane of the first optical component is outside the variable optic (10).
[2]
2. Optical system (1) according to claim 1, wherein the first optical component has a controllably variable focal length.
[3]
An optical system (1) for examining an eye (7), the optical system (1) comprising: an OCT system (2) configured to generate a measuring beam (9) which is incident on the eye (7 ) impinges; wherein the OCT system (2) comprises a lens (29) and a variable optics (10), wherein the variable optics (10), seen relative to an object-directed light path of the measuring beam (9), upstream of the lens (29) is arranged ; wherein the variable optic (10) comprises a first optical component having an optically active entrance surface through which the measuring beam (9), in the object directed light path, enters the variable optic (10) and wherein the first optical component further comprises a focal plane of a Main plane of an object-side beam output of the first optical component; wherein the variable optic (10) has a first configuration in which a focal plane position of the first optical component is within the variable optic (10); and wherein the first optical component has a controllably variable focal length.
[4]
The optical system (1) according to one of the preceding claims, wherein in the first configuration the variable optic (10) is a substantially afocal system.
[5]
5. Optical system (1) according to one of the preceding claims, wherein in the first configuration, a second optical component of the variable optics (10) images a point at the position of the focal plane of the first optical component on the object side substantially to infinity.
[6]
The optical system (1) according to any one of claims 1 to 4, wherein the variable optic (10) further comprises a second optical component disposed downstream of the first optical component relative to an object-directed light path of the measuring beam (9); wherein in the first configuration, a focal length of a principal plane of a light source side beam input of the second optical component is greater than 1.5 times a focal length of the main plane of the object side beam output of the first component.
[7]
7. An optical system according to claim 1, wherein the variable optic is further controllably configurable into a second configuration in which the position of the focal plane of the first component is outside the variable optic; wherein a focal length of the principal plane of the object-side beam output of the first optical component in the second configuration is greater than in the first configuration.
[8]
8. An optical system according to claim 1, wherein the optical system has a fixing light device for generating a fixation point for an eye, which is arranged at a position of an object distance from the objective, the object distance being between 50 millimeters and 400 millimeters.
[9]
9. An optical system (1) according to claim 8, wherein the OCT system (10) comprises a scanning system (30), wherein at a scan setting of the scanning system (30) an axis of the measuring beam (9) substantially parallel to a Sehache of the eye (7) runs when the eye (7) fixes the fixation point centrally.
[10]
The optical system according to claim 1, further comprising a microscopy system configured to generate an observation channel, wherein an image in an image plane is detected by means of the observation channel (41-1) is producible by an object area of the eye which is arranged in an object plane (40); wherein the observation channel (19-1) passes through the lens (29) and the object plane (40) is at the position of the object distance.
[11]
11. Optical system (1) according to one of the preceding claims, wherein a plurality of different focal plane positions are controllably adjustable by means of a control of the variable optics (10) for a main plane of an object-side beam output of the variable optics (10).
[12]
12. The optical system according to claim 1, wherein a focal length of a principal plane of an object-side beam exit of the variable optics is controllably adjustable to different values, wherein in each of the values, a focal plane position of the principal plane is substantially equal.
[13]
Optical system (1) according to one of the preceding claims, wherein the variable optics (10) are controllably adjustable in a plurality of substantially afocal configurations having different values of afocal beam expansion.
[14]
14. An optical system (1) according to claim 3, wherein a plurality of different focal plane positions are controllably adjustable by means of a control of the variable optics (10), for a main plane of an object-side beam output of the variable optics (10); and wherein the optical system is further configured such that, for at least one of the focal plane positions, the focal plane of the main plane of the object-side beam output of the variable optic (10) is controllably adjustable to different values, wherein each of the values is the focal plane position is substantially the same; and / or that the variable optics (10) are controllably adjustable in a plurality of substantially afocal configurations having different values of afocal beam expansion.
[15]
Optical system (1) according to one of the preceding claims, wherein the optical system (1) is configured or configurable such that the measuring beam (9) is incident on the variable optics (10) as a substantially parallel beam.
[16]
16. Optical system (1) according to one of claims 1 to 8 or 10 to 15, wherein the OCT system (2) has a scanning system (30) for scanning the measuring beam (9), wherein the scanning system (30), seen relative to an object-directed light path of the measuring beam (9), upstream of the variable optics (10) is arranged.
[17]
17. The optical system according to claim 1, wherein the OCT system has a scanning system for scanning the measuring beam, wherein the scanning system is viewed relative to an object-oriented scanning system Light path of the measuring beam (9), downstream of the variable optics (10) is arranged.
[18]
18. The optical system according to claim 1, wherein the variable optic has a first movable optical unit.
[19]
The optical system (1) according to claim 18, wherein the first movable optical unit (12) has a negative refractive power.
[20]
20. Optical system (1) according to one of the preceding claims, wherein the variable optics (10) comprises a second movable optical unit (11), wherein - the second movable optical unit (11) has a positive refractive power, and / or - Measuring beam through the second movable optical unit (11) enters the variable optics.
[21]
Optical system (1) according to one of the preceding claims, wherein the variable optics (10) comprises a first movable optical unit (12) and a second movable optical unit (11), wherein the first movable optical unit (12) has a negative Refractive power and the second movable optical unit (11) has a positive optical power; wherein, as seen relative to the object-directed light path of the measuring beam (9), the first movable optical unit (12) is disposed downstream of the second movable optical unit (11).
[22]
22. Optical system according to one of the preceding claims, wherein the variable optics has a further optical unit (13), wherein the further optical unit, seen relative to an object-directed light path of the measuring beam (9), - downstream of a first movable optical unit (12 ) is disposed of the variable optics, which has a negative refractive power, and / or - is arranged downstream of a second movable optical unit (11) of the variable optics, which has a positive refractive power; and / or - the measuring beam (9) leaves the variable optics (10) through the further optical unit (13); and / or - the further optical unit (13) has a positive refractive power; and / or - a position of a focal plane of a main plane of a light source side beam input of the further optical unit is arranged within the variable optical system (10).

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法律状态:

优先权:

---

申请号 | 申请日 | 专利标题

---

DE102014014182|2014-09-19|

---

PCT/EP2015/001872|WO2016041640A1|2014-09-19|2015-09-21|System for optical coherence tomography, comprising a zoomable kepler system|

---