Optical biopsy device

Abstract

An objective lens system for an optical biopsy device has a lens that comprises a first part configured for viewing at a first magnification, and a second part configured for viewing at a second magnification. The second magnification is substantially different from the first magnification. The first magnification enables viewing a larger area of a target and the second magnification enables viewing the target at a cellular level with high sensitivity and specificity. Combining viewing at two different magnifications in a single objective lens results in a compact optical biopsy device.

Claims

1. An objective lens system for an optical biopsy device having a single lens comprising: a first part configured for viewing at a first magnification, the first part having a first curvature, a second part configured for viewing at a second magnification, the second part having a second curvature different from the first curvature, wherein the first magnification is associated with a macroscopic view and the second magnification is associated with a microscopic view; and a rotational symmetric aspherical surface with a first sag, wherein the first part and the second part of the lens are concentric to each other and the second part substantially surrounds the first part, and wherein the rotational symmetric aspherical surface is common to the first part and the second part, wherein the first part has a first wavelength sensitive transmission coating that does not transmit any light from a first illumination source, and wherein the second part has a second wavelength sensitive transmission coating that does not transmit any light from a second illumination source.

2. The objective lens system of claim 1, wherein the relationship between the first curvature and the second curvature is defined as $.Math.\frac{c_2-c_1}{c_1}.Math.>0.05$ wherein c.sub.1 is the curvature of the first part and c.sub.2 is the curvature of the second part.

3. The objective lens system of claim 1, wherein the first curvature and the second curvature have different signs.

4. The objective lens system of claim 1, wherein the first magnification is at least 10 times smaller than the second magnification.

5. An optical biopsy device comprising: an inserting tube to be inserted into a body; and an objective lens system secured in a tip end of the inserting tube for viewing at a first magnification and for viewing at a second magnification, wherein the objective lens system comprises a single lens with a first part configured for viewing at the first magnification, a second part configured for viewing at the second magnification, and a rotational symmetric aspherical surface, wherein the first part and the second part of the lens are concentric to each other and the second part substantially surrounds the first part, wherein the rotational symmetric aspherical surface is common to the first part and the second part, and wherein the first part has a first curvature and the second part has a second curvature different from the first curvature, and wherein the first magnification is associated with a macroscopic view and the second magnification is associated with a microscopic view a first illumination source; and a second illumination source, wherein the first part has a first wavelength sensitive transmission coating that does not transmit any light from the first illumination source and the second part has a second wavelength sensitive transmission coating that does not transmit any light from the second illumination source.

6. The optical biopsy device as claimed in claim 5 further comprising an image sensor, wherein the image formed by the lens is relayed on to the image sensor.

7. The optical biopsy device as claimed in claim 5 further comprising: a fiber bundler configured for relaying an image formed by the lens; and a console optically coupled to the fiber bundler and configured for reading out the image formed.

8. The optical biopsy device as claimed in claim 5 further comprising: a single scanning fiber configured for reading out an image formed; and a console optically coupled to the single scanning fiber configured for reconstructing the image formed.

Description

BRIEF DESCRIPTION OF THE FIGURES

(1) These and other characteristics, features and advantages of the present invention will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate, by way of example, the principles of the invention. This description is given for the sake of example only, without limiting the scope of the invention. The reference figures quoted below refer to the attached drawings.

(2) FIG. 1 shows an objective lens system according an embodiment of the invention;

(3) FIG. 2a shows a ray trace of an image formed in a macroscopic view;

(4) FIG. 2b shows a ray trace of an image formed in a microscopic view;

(5) FIG. 3 shows an objective lens with a switchable diaphragm according to an embodiment of the invention;

(6) FIG. 4a shows an optical biopsy device according to an embodiment of the invention, where an image is formed in a macroscopic view and an image sensor is replaced by a fiber bundler;

(7) FIG. 4b shows an optical biopsy device according to an embodiment of the invention, where an image is formed in a microscopic view and an image sensor is replaced by a fiber bundler;

(8) FIG. 5 shows a schematic of a confocal scanning mechanism;

(9) FIG. 6a shows an optical biopsy device where an image sensor is replaced by a scanning fiber that readout the images in a macroscopic view; and

(10) FIG. 6b shows an optical biopsy device where an image sensor is replaced by a scanning fiber that readout the images in a microscopic view.

DETAILED DESCRIPTION OF THE INVENTION

(11) Particular and preferred aspects of the invention are set out in the accompanying independent and dependent claims. Features from the dependent claims may be combined with features of the independent claims and with features of other dependent claims as appropriate and not merely as explicitly set out in the claims.

(12) The present invention will be described with respect to particular embodiments and with reference to certain drawings but the invention is not limited thereto but only by the claims. Any reference signs in the claims shall not be construed as limiting the scope. The drawings described are only schematic and are non-limiting. In the drawings, the size of some of the elements may be exaggerated and not drawn on scale for illustrative purposes. Where the term “comprising” is used in the present description and claims, it does not exclude other elements or steps. Where an indefinite or definite article is used when referring to a singular noun e.g. “a” or “an”, “the”, this includes a plural of that noun unless something else is specifically stated.

(13) Furthermore, the terms first, second, third and the like in the description and in the claims, are used for distinguishing between similar elements and not necessarily for describing a sequential or chronological order. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other sequences than described or illustrated herein.

(14) Moreover, the terms top, bottom, over, under and the like in the description and the claims are used for descriptive purposes and not necessarily for describing relative positions. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other orientations than described or illustrated herein.

(15) In the context of the invention, target can be any interior region including lung, bladder, abdominal cavity, knee joint and the like. The examining physician could examine the interior region and upon noticing a suspicious region i.e. a lesion, he can view in situ the single cells of the lesion. In the same context, macroscopic view refers to viewing a larger area of the target and microscopic viewing refers to viewing the target at a cellular level with high sensitivity.

(16) FIG. 1 shows an objective lens system 100 with an optical axis 150 according to the invention. It consists of one lens as shown in this example. The lens 100 has a first part 120 with an aperture radius R.sub.1 and a second part 110 with an aperture radius R.sub.2. The first part 120 of the lens surface is used to form the image of a target being imaged in a macroscopic view and the second part 110 is used to form the image of the target in a microscopic view. Surface 130 is the rotational symmetric aspherical surface of the objective lens 100.

(17) FIG. 2a shows a ray trace plot showing the macroscopic view of a target (not shown) placed at an object plane 20 where the first part 120 of the objective lens system 100 is used. FIG. 2b shows a ray trace plot showing the microscopic view of the target where the second part 110 of the objective lens system 100 is used. The image is formed on an image sensor 30. A protective glass plate 25 is placed before the objective lens 100.

(18) FIG. 3 shows an objective lens system 100 with an optical axis 150 and a switchable diaphragm 200. The diaphragm consists of two parts: an inner part 210 and an outer part 220. Each of these parts can be switched to a transparent state or to a light absorbing state.

(19) FIGS. 4a and 4b show an optical biopsy device 1 including an objective lens system 100, where an image sensor is replaced by a fiber bundler 80. The objective lens system 100 transforms a beam 40, 50 emerging from a target (not shown) into a beam 42, 52 and forms an image onto one end of the fiber bundler 80. The image is relayed to the other end of the fiber bundler 80 and is probed by the beam 420 of a console 410.

(20) FIG. 5 shows a confocal scanning system as described in J. Vasc. Res. 2004; 41:400-411 by E. Laemmel et al. 1 is a tissue sample. 2 is an image bundler. 3 is a lens. 4 is a tilting mirror. 5 is a dichroic filter. 6 is a laser source. 7 is a photo detector.

(21) FIG. 6 shows an optical biopsy device 1 including an objective lens system 100 where the image sensor is replaced by a scanning fiber 500 that reads out the images. This fiber 500 is connected to a console (not shown). The objective lens system 100 transforms a beam 40, 50 emerging from a target (not shown) into a beam 42, 52. By scanning the fiber end 510, the image formed can be readout and transferred to the console.

(22) As shown in FIG. 1, the objective lens system 100 comprises two parts 120 and 110. The first part 120 of the surface has a best-fit curvature c.sub.1 of the best-fit sphere of that part of the surface and the second part 110 of the surface has a best-fit curvature c.sub.2 of the best-fit sphere of that part of the surface. c.sub.1 and c.sub.2 are substantially different.

(23) The rotational symmetric aspherical surface 130 is given by the equation

(24) $\begin{array}{cc}z\left(r\right)=\frac{{\mathrm{cr}}^2}{1+\sqrt{1-c^2{r}^2}}+\underset{i=2}{\overset{5}{.Math.}}{B}_{2i}{r}^{2i}& \left(1\right)\end{array}$

(25) where z is the position of the surface in the direction of the optical axis 150 in millimeters, r is the distance to the optical axis in millimeters, c is the curvature (the reciprocal of the radius) of the surface and B.sub.4 to B.sub.10 are the coefficients of the i-th power of r. The value of c is 1.096014 mm.sup.−1. The values of the coefficients B.sub.4 to B.sub.10 are 0.73894797, −8.5560965, 38.136909 and −40.046541, respectively.

(26) The first part 120 of the objective lens system 100 is also described by equation (1) but with the coefficients given by c is 0.5635876 mm.sup.−1 and the values of the coefficients B.sub.4 to B.sub.10 are 0.6048722, −10.82945, 105.297 and 84.06069 respectively. The point z(0) of this surface lies at 0.5 mm distance along the optical axis from the z(0) point of the surface 130. Furthermore, the aperture radius R.sub.1 is 0.2 mm. The second part 110 is also described by equation (1) but with the coefficients given by c is −1.777857 mm.sup.−1 and the values of the coefficients B.sub.4 to B.sub.10 are 1.122886, 10.22766, −69.06088, and 218.1365, respectively. The point z(0) of this surface lies also at 0.5 mm distance along the optical axis from the z(0) point of the surface 130. Furthermore, the aperture radius R.sub.2 is 0.45 mm. The material of the lens has refractive index of 1.581 at 650 nm wavelength and the Abbe number 29.9. The glass plate 25 in front of the lens has a thickness of 0.1 mm and refractive index of 1.515 at a wavelength of 650 nm and the Abbe number is 64.2.

(27) To determine the best-fit radii of the first part 120 and second part 110, the best-fit sphere approach is used. The best-fit sphere is determined by finding the radius of the sphere that minimizes the root-means-square (RMS) deviation between the surface sag and the sag of the best-fit sphere. For the first part 120, the best-fit sphere radius is 1.695 mm. For the second part 110, the best-fit radius is −0.813 mm. A positive radius means that the center of the sphere lies to the right of the surface and a negative sign means that the center of the sphere lies to the left of the surface. The reciprocal of these best-fit radii are then the best-fit curvatures of the surfaces. For the first part 120, the best-fit curvature c.sub.1 is then 0.590 mm.sup.−1 and for the second part 110, c.sub.2 is −1.230 mm.sup.−1. A preferable criterion to define the difference between c.sub.1 and c.sub.2 is that the mod of the ratio of (c.sub.2−c.sub.1) to c.sub.1 should be greater than 0.05

(28) $.Math.\frac{c_2-c_1}{c_1}.Math.>0.05$
It is further preferable if

(29) $\frac{c_2}{c_1}<0$
i.e., the curvatures of first and second part should have different signs.

(30) In the above example the target in the macroscopic view is positioned at 50.5 mm distance from the protective glass plate 25, while the image sensor is at a distance of 2.0 mm from the objective lens system 100. The magnification in this configuration is 0.054. In the microscopic view, the object is positioned at a distance of 0.5 mm from the protective glass plate 25. The magnification is 2.248. The magnification factor between the two modes is 41.6. In general it is preferable that the magnification factor between the two modes is larger than 10. It would be further advantageous to have a magnification factor as high as 40.

(31) The first part 120 and the second part 110 of the objective lens system 100 are preferably coated with two different coatings that are sensitive to different wavelengths to form images in both macroscopic and microscopic modes. Along with these two coatings, two illumination sources with corresponding wavelengths are used. When illumination is with the first source, the coating on the second part of the lens does not transmit the light of the first source and the first part of the lens forms an image in the first viewing mode. When illumination is with the second source, the coating on the first part of the lens does not transmit the light of the second source and the second part of the lens forms an image in the second viewing mode. The ray trace plots in FIGS. 2a and 2b illustrate this.

(32) According to another embodiment as shown in FIG. 3, a switchable diaphragm 200 is used to form images in different modes. The diaphragm consists of two parts: the inner part 210 and the outer part 220. Each of these parts can be switched to a transparent state or to a light absorbing state. In the first viewing mode the inner part 210 is made transparent and the outer part 220 is made opaque. In the second viewing mode the situation is reversed. The opaque part does not transmit light whereas the transparent part forms an image. The diaphragm can be made of liquid crystal diaphragm. Another possibility is to make use of a switchable diaphragm based on the electro-wetting principle as described in EP-A-1543370. The switching can also be based on a liquid crystal principle well known in the liquid crystal based displays.

(33) In all the above-mentioned embodiments, the image is formed on the image sensor 30. To make the design of the optical device simpler, relaying the image using a fiber bundle technique as described for instance in J. Vasc. Res. 2004; 41:400-411 by E. Laemmel et al. is preferably employed. Instead of imaging onto an image sensor 30, it is now imaged on one end of a fiber bundler 80 as shown in FIGS. 4a and 4b. This fiber bundler 80 consists of many tiny fibers. The image is then relayed by this fiber bundler to the other end of the fiber bundler 80. The other end of the fiber can now be probed by the beam 420 of the console 410. An example of such a console 410 is for instance a confocal scanning system as shown in FIG. 5 and as described in J. Vasc. Res. 2004; 41:400-411 by E. Laemmel et al. This reference shows an example of the scanning system 410 and 420 of FIG. 4 to read out the relayed image by the fiber bundler 80.

(34) In a further embodiment, as shown in FIGS. 6a and 6b, a single scanning fiber 500 is used for relaying the image formed. This fiber 500 is connected to a console (not shown). By scanning the fiber end 510, the image formed by the optical probe can be readout and transferred to the console as described in US-A-20050052753.

(35) It is to be understood that although preferred embodiments, specific constructions and configurations, as well as materials, have been discussed herein for devices according to the present invention, various changes or modifications in form and detail may be made without departing from the scope and spirit of this invention.