Patent Grant
7821720
This invention relates generally to lens systems, and more particularly to an endoscope objective lens suitable for collecting white light and fluorescence images, where the numerical aperture and entrance pupil diameter is large to allow higher collection power for weak fluorescence signal, while maintaining a small overall diameter.
Conventionally, endoscopes are utilized for places that are difficult to see directly, especially inside human bodies. As its objective lens system, various kinds constituted of multiple lens elements are known.
While conventional retrofocus lens systems for endoscopy cover a large field of view, this type of arrangement usually has a small entrance pupil diameter in order to minimize third order aberrations at large field and thus maintain high optical performance. Although this is normally adequate for bright field imaging, it is not optimized for fluorescence, where the typical fluorescence signal strength is substantially weaker than the white light image. The small entrance pupil means that the collection efficiency of the objective is very weak. It is advantageous for an objective intended for dual modality imaging to have improved collection power, maintain a small overall diameter, large FFOV, easy of manufacturing and high optical resolution for both visible and near infrared wavelength.
Briefly, an endoscope objective lens comprises a negative lens group, G1; a positive lens group, G2; and a stop, S, placed between the negative lens group, G1, and the positive lens group, G2, wherein the following conditions (1) to (4) are satisfied:
0.5≦EFL≦1.4 mm, −4≦F1/EFL≦−1.2, 1.1≦F2/EFL≦1.9 (1)
F#≦4.2, (2)
EPD≧0.4 mm, 0.4≧EPD/Dia≧0.2 (3)
FFOV≧120° (4)
and wherein,
EFL is the effective focal length of the objective lens,
F1 is the effective focal length of the positive lens group, G1,
F2 is the effective focal length of the negative lens group, G2,
F# is the f number of the objective lens,
EPD is the entrance pupil diameter of the objective lens,
Dia is the maximum diameter of the objective lens, and
FFOV is the full field of view of the objective lens.
These and other features, aspects, and advantages of the present invention will become better understood when the following detailed description is read with reference to the accompanying drawings in which like characters represent like parts throughout the drawings, wherein:
Referring to the drawings wherein identical reference numerals denote the same elements throughout the various views,
In general, the endoscope objective lens of the invention comprises a negative lens group, G1, a positive lens group, G2, and a stop, S, placed between the negative lens group, G1, and the positive lens group, G2. The endoscope objective lens of the invention satisfies the following Conditional Expressions:
0.5≦EFL≦1.4 mm, −4≦F1/EFL≦−1.2, 1.1≦F2/EFL≦1.9 (1)
F#≦4.2, (2)
EPD≧0.4 mm, 0.4≧EPD/Dia≧0.2 (3)
FFOV≧120° (4)
wherein,
EFL is the effective focal length of the objective lens,
F1 is the effective focal length of the positive lens group, G1,
F2 is the effective focal length of the negative lens group, G2,
F# is the f number of the objective lens,
EPD is the entrance pupil diameter of the objective lens,
Dia is the maximum diameter of the objective lens, and
FFOV is the full field of view of the objective lens.
In the event that fluorescence imaging is performed in the near infrared, the wavelength range objective lens needs to extend beyond the visible spectrum. It is preferable for the objective to be able to cover a spectrum of between about 400 nm-850 nm, and more preferably between about 400 nm-1970 nm, as shown in Example 4.
In order to achieve high resolution imaging, the optical resolution of the system needs to match the pixel size of the detector, or ˜3.6 μm assuming a ⅙″ detector. At 850 nm, the F# required for the objective to produce a 3.6 μm rms spot diameter is preferably F#≦4.2, and more preferably ≦2.8 to produce sharp images, especially for near infrared light.
For endoscopy applications, the angular field coverage is preferred to be as large as possible to allow the maximum observation of the lumen. The FFOV is greater than or equal to 120°, and preferably FFOV≧170°.
The dual modality use of the objective requires the objective to have a means to fully reject the excitation light to avoid overwhelming the weak fluorescence signal. This requires at least one (preferably two) optical filter disposed between the last lens element of the objective and the detector. Such an optical filter, typically an interference type laser rejection filter, is made on glass with finite thickness, usually greater than or equal to 0.7 mm.
Due to the large angle of rays transmitted through the filter, the passband of the laser rejection filter may shift up to 2% of the central bandwidth. This requires the optical filter to have a passband full width at half maximum (FWHM) in the range of 10-50 nm.
In an alternative embodiment, a second laser optical filter, such as a laser rejection filter, and the like, is tilted by ≧10° in order to prevent any multiple reflection between the two filters.
The optical filter, F, may comprises a laser rejection filter, such as a volume holographic filter, a thin film dielectric filter, dichroic filter, a polarization interference filter, an air spaced or solid spaced etalon.
In an alternative embodiment, in addition to the optical filter, F, a tunable filter, such as a liquid crystal etalon or a liquid crystal tunable polarization interference filter, can be used adjunct with a monochromatic CCD for multi-spectral imaging or hyperspectral imaging endoscope such that the center wavelength of the tunable filter matches relevant excitation wavelengths. This tunable filter allows for the possible identification and distinction of multiple fluorescence dye stained tissues. For example, the center wavelength of the tunable filter can be in the range between about 600-800 nm.
Spherical surfaces are preferred in the embodiment for manufacturing considerations. However, this does not exclude usage of aspherical surfaces or plastic inject molded elements in the design.
Below, the endoscope objective lens of the invention is further explained employing concrete examples.
The schematic constitution of an endoscope objective lens of Example 1 is shown in
Radius of curvature R (mm) of each lens surface, thickness or air gap (mm) between lenses, glass code, and semi-aperture are listed in Table I. Note that numbers in the table indicate the order from the object side. Also, as shown in Table I, the Conditions Expressions (1) to (4) are all satisfied.
The schematic constitution of an endoscope objective lens of Example 2 is shown in
Radius of curvature R (mm) of each lens surface, thickness or air gap (mm) between lenses, glass code, and semi-aperture are listed in TABLE II. Note that numbers in the table indicate the order from the object side. Also, as shown in TABLE II, the Conditions Expressions (1) to (4) are all satisfied.
The schematic constitution of an endoscope objective lens of Example 3 is shown in
Radius of curvature R (mm) of each lens surface, thickness or air gap (mm) between lenses, glass code, and semi-aperture are listed in TABLE III. Note that numbers in the table indicate the order from the object side. Also, as shown in TABLE III, the Conditions Expressions (1) to (4) are all satisfied.
The schematic constitution of an endoscope objective lens of Example 4 is shown in
Radius of curvature R (mm) of each lens surface, thickness or air gap (mm) between lenses, glass code, and semi-aperture are listed in TABLE IV. Note that numbers in the table indicate the order from the object side. Also, as shown in TABLE IV, the Conditions Expressions (1) to (4) are all satisfied.
The schematic constitution of an endoscope objective lens of Example 5 is shown in
Radius of curvature R (mm) of each lens surface, thickness or air gap (mm) between lenses, glass code, and semi-aperture are listed in TABLE V. Note that numbers in the table indicate the order from the object side. Also, as shown in TABLE V, the Conditions Expressions (1) to (4) are all satisfied.
The schematic constitution of an endoscope objective lens of Example 6 is shown in
Radius of curvature R (mm) of each lens surface, thickness or air gap (mm) between lenses, glass code, and semi-aperture are listed in TABLE VI. Note that numbers in the table indicate the order from the object side. Also, as shown in TABLE VI, the Conditions Expressions (1) to (4) are all satisfied.
According to an alternate embodiment, the endoscope objective lens 10 may include a tunable filter, TF, as shown in
The endoscope objective lens of the invention has about four (4) times higher collection power as compared with the prior art because the collection power is proportional to the square of the EPD. The ratio between the EPD and the outer dimension of the largest element is a good indicator of the effectiveness of using the maximum allowable diameter for collecting light. This ratio is generally small (<0.15), as compared to ≧0.2 in the invention.
This written description uses examples to disclose the invention, including the best mode, and also to enable any person skilled in the art to make and use the invention. The patentable scope of the invention is defined by the claims, and may include other examples that occur to those skilled in the art. Such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims, or if they include equivalent structural elements with insubstantial differences from the literal languages of the claims.
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