JP2007249189A - Objective lens for endoscope - Google Patents
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- JP2007249189A JP2007249189A JP2007031678A JP2007031678A JP2007249189A JP 2007249189 A JP2007249189 A JP 2007249189A JP 2007031678 A JP2007031678 A JP 2007031678A JP 2007031678 A JP2007031678 A JP 2007031678A JP 2007249189 A JP2007249189 A JP 2007249189A
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Abstract
Description
本発明は、内視鏡の先端部に設けられる対物レンズに関し、特に、その像面側に光路変換プリズムが配置されるような長いバックフォーカスを有する光学系に対応可能な内視鏡用対物レンズに関する。
BACKGROUND OF THE
従来より、先端部において、ＣＣＤ（Charge Coupled Device）などの固体撮像素子を長手方向に対し平行に配置した構成の内視鏡が知られている。図２３はその内視鏡における対物光学系の概略を示している。図２３に示したように、固体撮像素子２００が内視鏡の先端部において軸方向（長手方向）Ｚに対し平行に配置されている。そして、その対物レンズ１００と固体撮像素子２００との間にカバーガラス１０１を介して光路変換プリズム１０２が挿入配置されるようになっている。対物レンズ１００の光軸Ｚ１は、光路変換プリズム１０２によって、固体撮像素子２００の方向に略９０度折り曲げられる。この光路変換プリズム１０２の大きさはイメージサイズで決まり、光路変換プリズム１０２が挿入配置される対物レンズ１００の最終面から結像位置Ｐまでの距離（ほぼ、バックフォーカスと同等）を十分に確保しておく必要がある。このため、全系の焦点距離に比べてバックフォーカスの長い対物レンズが必要とされている。しかしながら、内視鏡用の対物レンズは、その広角化の要請に伴い、イメージサイズが同一でも焦点距離は短くなる傾向にあり、十分なバックフォーカスを得ることは困難であった。
2. Description of the Related Art Conventionally, an endoscope having a configuration in which a solid-state imaging device such as a CCD (Charge Coupled Device) is arranged in parallel with a longitudinal direction at a distal end portion is known. FIG. 23 shows an outline of an objective optical system in the endoscope. As shown in FIG. 23, the solid-
本願出願人は、特許文献１ないし特許文献３において４群５構成の内視鏡用対物レンズを提案している。特に特許文献３では、バックフォーカスが全系の合成焦点距離ｆに比べ２倍よりも長い十分なバックフォーカスを確保した内視鏡用対物レンズを提案している。
一方、内視鏡用対物レンズは被写界深度を深くするためにＦ値の暗いものが多く、球面収差やコマ収差が画質を決める重要な要因となることは少なく、画質劣化の大きな要因として倍率色収差が挙げられる。特に近年では、固体撮像素子の高密度化が進み、画素数が増大するにつれ、倍率色収差の十分な補正が必要とされている。倍率色収差を補正するには、絞りより離れた位置に倍率色収差補正を担う光学部材が配置されていることが好ましい。特に絞りより像側では、結像面に近い位置に倍率色収差補正を担う光学部材が配置されているほど、その効果がより顕著である。しかしながら、バックフォーカスの長いレンズ系においては、結像面に近い位置に光学部材が存在せず、倍率色収差の補正は容易ではなかった。上記各特許文献に記載の内視鏡用対物レンズは、倍率色収差の補正の点でまだ改善の余地がある。 On the other hand, many objective lenses for endoscopes have a dark F value in order to increase the depth of field, and spherical aberration and coma are rarely important factors that determine image quality. A lateral chromatic aberration is mentioned. Particularly in recent years, as the density of solid-state imaging devices has increased and the number of pixels has increased, sufficient correction of lateral chromatic aberration has been required. In order to correct lateral chromatic aberration, it is preferable that an optical member for correcting lateral chromatic aberration is disposed at a position away from the stop. In particular, on the image side from the stop, the effect is more remarkable as the optical member for correcting the chromatic aberration of magnification is arranged at a position closer to the imaging surface. However, in a lens system with a long back focus, there is no optical member at a position close to the image plane, and it is not easy to correct lateral chromatic aberration. The endoscope objective lenses described in the above patent documents still have room for improvement in terms of correcting the lateral chromatic aberration.
本発明はかかる問題点に鑑みてなされたもので、その目的は、像面側に光路変換プリズムを挿入配置することが可能な十分な長さのバックフォーカスを確保しつつ、倍率色収差を良好に補正することができるようにした内視鏡用対物レンズを提供することにある。 The present invention has been made in view of such problems, and its purpose is to improve the lateral chromatic aberration while ensuring a sufficiently long back focus capable of inserting and arranging an optical path conversion prism on the image plane side. An object of the present invention is to provide an endoscope objective lens that can be corrected.
本発明による内視鏡用対物レンズは、物体側から順に、像面側の面が凹面とされた負の第１レンズと、像面側の面が平面または物体側の面に比べて曲率半径の絶対値が大きい面とされた正の第２レンズと、物体側の面が平面または像面側の面に比べて曲率半径の絶対値が大きい面とされた正の第３レンズと、物体側の面が平面または像面側の面に比べて曲率半径の絶対値が大きい面とされた正の第４レンズおよび負のメニスカス形状の第５レンズからなり全体で正の屈折力を有する接合レンズとが配設されると共に、第２レンズと第３レンズとの間に明るさ絞りが配置され、全系のバックフォーカスが全系の合成焦点距離の２倍よりも長く、かつ、下記条件式を満足するように構成されているものである。
（ν2＋ν5）＜４５ ……（１）
ただし、ν2は第２レンズのアッベ数、ν5は第５レンズのアッベ数とする。
An endoscope objective lens according to the present invention includes, in order from the object side, a negative first lens whose surface on the image surface side is a concave surface, and a radius of curvature as compared with a surface on the image surface side or a surface on the object side. A positive second lens whose surface has a large absolute value, a positive third lens whose surface on the object side is a flat surface or a surface whose absolute value of curvature radius is larger than that of the surface on the image surface side, and an object A cemented surface having a positive refractive power as a whole comprising a positive fourth lens and a negative meniscus fifth lens whose side surface is a plane or a surface having a larger absolute value of the radius of curvature than a plane or image side surface And an aperture stop between the second lens and the third lens, the back focus of the entire system is longer than twice the combined focal length of the entire system, and the following conditions It is comprised so that a formula may be satisfied.
(Ν 2 + ν 5 ) <45 (1)
Here, ν 2 is the Abbe number of the second lens, and ν 5 is the Abbe number of the fifth lens.
本発明による内視鏡用対物レンズでは、最も像面側に倍率色収差補正を担う光学部材として接合レンズを配置し、さらに条件式（１）を満足して、明るさ絞りに対して物体側にある正の第２レンズと明るさ絞りに対して像面側にありかつ最も像面に近い位置にある負の第５レンズとのアッベ数を小さく抑えることで、全系のバックフォーカスを全系の合成焦点距離の２倍よりも長くして像面側に光路変換プリズムを挿入配置することが可能な十分な長さのバックフォーカスを確保しつつ、倍率色収差が良好に補正される。 In the endoscope objective lens according to the present invention, a cemented lens is disposed as an optical member for correcting chromatic aberration of magnification closest to the image plane side, further satisfies the conditional expression (1), and is located on the object side with respect to the aperture stop. By keeping the Abbe number between a certain positive second lens and the negative fifth lens closest to the image plane on the image plane side with respect to the aperture stop, the entire back focus of the entire system is reduced. The lateral chromatic aberration is corrected well while ensuring a back focus having a length sufficient to allow the optical path conversion prism to be inserted and disposed on the image plane side longer than twice the combined focal length.
本発明による内視鏡用対物レンズにおいて、さらに条件式（２）を満足することが好ましい。条件式（２）を満足することで、十分な長さのバックフォーカスの確保と倍率色収差の補正とをさらにし易くなる。
ｆ2×（ν5−ν4）／｛ＲA・（Ｂｆ＋Ｄ5／ｎ5）｝≧１０ ……（２）
ただし、ｆは全系の合成焦点距離、Ｂｆは全系のバックフォーカス、ν4は第４レンズのアッベ数、ν5は第５レンズのアッベ数、ＲAは第４レンズと第５レンズとの接合面の曲率半径、Ｄ5は第５レンズの中心厚、ｎ5は第５レンズの屈折率とする。
In the endoscope objective lens according to the present invention, it is preferable that the conditional expression (2) is further satisfied. Satisfying conditional expression (2) makes it easier to secure a sufficiently long back focus and correct lateral chromatic aberration.
f 2 × (ν 5 −ν 4 ) / {R A · (Bf + D 5 / n 5 )} ≧ 10 (2)
Where f is the total focal length of the entire system, Bf is the back focus of the entire system, ν 4 is the Abbe number of the fourth lens, ν 5 is the Abbe number of the fifth lens, and R A is the fourth lens and the fifth lens. , D 5 is the center thickness of the fifth lens, and n 5 is the refractive index of the fifth lens.
本発明の内視鏡用対物レンズによれば、全系のバックフォーカスが全系の合成焦点距離の２倍よりも長い内視鏡用対物レンズであって、最も像面側に倍率色収差補正を担う光学部材として接合レンズを配置し、さらに条件式（１）を満足して、明るさ絞りに対して物体側にある正の第２レンズと明るさ絞りに対して像面側にありかつ最も像面に近い位置にある負の第５レンズとのアッベ数を小さく抑えるようにしたので、像面側に光路変換プリズムを挿入配置することが可能な十分な長さのバックフォーカスを確保しつつ、倍率色収差を良好に補正することができる。 According to the endoscope objective lens of the present invention, the back focus of the entire system is an endoscope objective lens that is longer than twice the combined focal length of the entire system, and the lateral chromatic aberration correction is performed on the most image side. A cemented lens is disposed as an optical member to be held, and further satisfies the conditional expression (1). The positive second lens on the object side with respect to the aperture stop and the image surface side with respect to the aperture stop are the most. Since the Abbe number with the negative fifth lens located close to the image plane is kept small, it is possible to secure a sufficiently long back focus capable of inserting and arranging the optical path conversion prism on the image plane side. The chromatic aberration of magnification can be corrected satisfactorily.
以下、本発明の実施の形態について図面を参照して詳細に説明する。
図１は、本発明の一実施の形態に係る内視鏡用対物レンズの第１の構成例を示している。この構成例は、後述の第１の数値実施例（図７）のレンズ構成に対応している。図２は、第２の構成例を示している。この構成例は、後述の第２の数値実施例（図８）のレンズ構成に対応している。図３は、第３の構成例を示している。この構成例は、後述の第３の数値実施例（図９）のレンズ構成に対応している。図４は、第４の構成例を示している。この構成例は、後述の第４の数値実施例（図１０）のレンズ構成に対応している。図５は、第５の構成例を示している。この構成例は、後述の第５の数値実施例（図１１）のレンズ構成に対応している。図６は、第６の構成例を示している。この構成例は、後述の第６の数値実施例（図１２）のレンズ構成に対応している。図１ないし図６において、符号Ｒｉは、最も物体側の構成要素の面を１番目として、像面側（結像側）に向かうに従い順次増加するようにして符号を付したｉ番目の面の曲率半径を示す。符号Ｄｉは、ｉ番目の面とｉ＋１番目の面との光軸Ｚ１上の面間隔を示す。なお、各構成例共に基本的な構成は同じなので、以下では図１に示した第１の構成例を基本にして説明する。
Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
FIG. 1 shows a first configuration example of an endoscope objective lens according to an embodiment of the present invention. This configuration example corresponds to the lens configuration of a first numerical example (FIG. 7) described later. FIG. 2 shows a second configuration example. This configuration example corresponds to the lens configuration of a second numerical example (FIG. 8) described later. FIG. 3 shows a third configuration example. This configuration example corresponds to the lens configuration of a third numerical example (FIG. 9) described later. FIG. 4 shows a fourth configuration example. This configuration example corresponds to the lens configuration of a fourth numerical example (FIG. 10) described later. FIG. 5 shows a fifth configuration example. This configuration example corresponds to the lens configuration of a fifth numerical example (FIG. 11) described later. FIG. 6 shows a sixth configuration example. This configuration example corresponds to a lens configuration of a sixth numerical example (FIG. 12) described later. In FIG. 1 to FIG. 6, the reference symbol Ri denotes the i-th surface with the reference symbol so that the surface of the component closest to the object side is the first and increases sequentially toward the image surface side (image formation side). Indicates the radius of curvature. The symbol Di indicates the surface interval on the optical axis Z1 between the i-th surface and the i + 1-th surface. Since the basic configuration is the same for each configuration example, the following description is based on the first configuration example shown in FIG.
この内視鏡用対物レンズは、内視鏡の先端部に設けられ、特に、固体撮像素子が軸方向（長手方向）に対し平行に配置された内視鏡（図２３参照）の対物レンズとして好適に使用されるものである。この内視鏡用対物レンズは、光軸Ｚ１に沿って物体側から順に、負の第１レンズＬ１と、正の第２レンズＬ２と、明るさ絞りＳｔと、正の第３レンズＬ３と、正の第４レンズＬ４および負の第５レンズＬ５からなる接合レンズＬ４５とを備え、全体として４群５枚のレンズ構成とされている。この内視鏡用対物レンズの像面側には、光路変換プリズムＧＰが配置され、さらに、この光路変換プリズムＧＰの像面側近傍にＣＣＤなどの固体撮像素子が配置される。光路変換プリズムＧＰと固体撮像素子との間には、カバーガラスなどのその他の光学部材が配置されることもある。なお、図１〜図６においてＰは結像位置を示す。図１〜図６では、光路変換プリズムＧＰを等価的に入射光軸Ｚ１と同一方向に展開し、結像位置Ｐが入射光軸Ｚ１と同一方向となるように図示しているが、実際には図２３に示した構成例と同様に、光路変換プリズムＧＰによって光路が略９０度折り曲げられるような構成となっている。 This endoscope objective lens is provided at the distal end of the endoscope, and in particular, as an objective lens for an endoscope (see FIG. 23) in which a solid-state imaging device is arranged in parallel to the axial direction (longitudinal direction). It is preferably used. The endoscope objective lens includes, in order from the object side along the optical axis Z1, a negative first lens L1, a positive second lens L2, an aperture stop St, a positive third lens L3, A cemented lens L45 including a positive fourth lens L4 and a negative fifth lens L5 is provided, and the lens configuration of the four groups is five as a whole. An optical path conversion prism GP is disposed on the image plane side of the endoscope objective lens, and a solid-state imaging device such as a CCD is disposed near the image plane side of the optical path conversion prism GP. Other optical members such as a cover glass may be disposed between the optical path conversion prism GP and the solid-state imaging device. In FIG. 1 to FIG. 6, P represents an image forming position. 1 to 6, the optical path conversion prism GP is equivalently developed in the same direction as the incident optical axis Z1, and the imaging position P is illustrated in the same direction as the incident optical axis Z1. As in the configuration example shown in FIG. 23, the optical path is bent by approximately 90 degrees by the optical path conversion prism GP.
第１レンズＬ１は、像面側の面が凹面とされた負レンズとなっている。第１レンズＬ１は、物体側の面が例えば平面とされた平凹レンズとされている。第２レンズＬ２は、像面側の面が平面または物体側の面に比べて曲率半径の絶対値が大きい面とされた正レンズとなっている。図１、図３、図４および図６の第１、第３、第４および第６の構成例では、第２レンズＬ２の像面側の面が平面とされた平凸レンズとされている。図２の第２の構成例および図５の第５の構成例では、第２レンズＬ２の像面側の面が物体側の面に比べて曲率半径の絶対値が大きい面とされている。特に第２の構成例は、第２レンズＬ２が物体側に凸面を向けたメニスカス形状の正レンズとなっている。また第５の構成例は、第２レンズＬ２が両凸レンズとなっている。 The first lens L1 is a negative lens having a concave surface on the image plane side. The first lens L1 is a plano-concave lens whose surface on the object side is a flat surface, for example. The second lens L2 is a positive lens in which the surface on the image plane side is a plane or a surface having a larger absolute value of the radius of curvature than the surface on the object side. In the first, third, fourth, and sixth configuration examples of FIGS. 1, 3, 4, and 6, the plano-convex lens is configured such that the image plane side surface of the second lens L2 is a flat surface. In the second configuration example in FIG. 2 and the fifth configuration example in FIG. 5, the surface on the image plane side of the second lens L <b> 2 has a larger absolute value of the radius of curvature than the surface on the object side. In particular, in the second configuration example, the second lens L2 is a meniscus positive lens having a convex surface facing the object side. In the fifth configuration example, the second lens L2 is a biconvex lens.
第３レンズＬ３は、物体側の面が平面または像面側の面に比べて曲率半径の絶対値が大きい面とされた正レンズとなっている。図１、図２および図４の第１、第２および第４の構成例では、第３レンズＬ３の物体側の面の面が平面とされた平凸レンズとされている。図３、図５および図６の第３、第５および第６の構成例では、第３レンズＬ３の物体側の面が像面側の面に比べて曲率半径の絶対値が大きい面とされ、像面側に凸面を向けたメニスカス形状の正レンズとなっている。 The third lens L3 is a positive lens in which the object-side surface is a flat surface or a surface having a larger radius of curvature than the image-side surface. In the first, second, and fourth configuration examples of FIGS. 1, 2, and 4, the plano-convex lens is configured such that the object-side surface of the third lens L3 is a flat surface. In the third, fifth, and sixth configuration examples of FIGS. 3, 5, and 6, the object-side surface of the third lens L <b> 3 is a surface that has a larger absolute value of the radius of curvature than the image-side surface. This is a meniscus positive lens with a convex surface facing the image surface side.
接合レンズＬ４５は、全体で正の屈折力を有している。第４レンズＬ４は、物体側の面が平面または像面側の面に比べて曲率半径の絶対値が大きい面とされた正レンズとなっている。第５レンズＬ５はメニスカス形状の負レンズとなっている。図１の第１の構成例では、第４レンズＬ４の物体側の面の面が平面とされた平凸レンズとされている。図２〜図６の第２ないし第６の構成例では、第４レンズＬ４の物体側の面が像面側の面に比べて曲率半径の絶対値が大きい面とされた両凸レンズとなっている。 The cemented lens L45 has a positive refractive power as a whole. The fourth lens L4 is a positive lens in which the object side surface is a flat surface or a surface with a larger absolute value of the radius of curvature than the image surface side surface. The fifth lens L5 is a meniscus negative lens. In the first configuration example of FIG. 1, the fourth lens L4 is a plano-convex lens in which the object-side surface is a flat surface. 2 to 6, the object side surface of the fourth lens L4 is a biconvex lens in which the absolute value of the radius of curvature is larger than that of the image side surface. Yes.
この内視鏡用対物レンズは、全系のバックフォーカスＢｆが全系の合成焦点距離ｆの２倍よりも長く構成されており、さらに以下の条件を満足している。ただし、ν2は第２レンズＬ２のアッベ数、ν5は第５レンズＬ５のアッベ数とする。
（ν2＋ν5）＜４５ ……（１）
この条件式の上限は以下の値であることが倍率色収差補正の点でより好ましい。
（ν2＋ν5）＜４０ ……（１Ａ）
This endoscope objective lens is configured such that the back focus Bf of the entire system is longer than twice the combined focal length f of the entire system, and further satisfies the following conditions. Here, ν 2 is the Abbe number of the second lens L2, and ν 5 is the Abbe number of the fifth lens L5.
(Ν 2 + ν 5 ) <45 (1)
The upper limit of this conditional expression is more preferably the following value in terms of correcting chromatic aberration of magnification.
(Ν 2 + ν 5 ) <40 (1A)
また、この内視鏡用対物レンズは、接合レンズＬ４５に関し下記条件式を満足することが好ましい。ただし、ν4は第４レンズＬ４のアッベ数、ν5は第５レンズＬ５のアッベ数、ＲAは第４レンズと第５レンズとの接合面の曲率半径、Ｄ5は第５レンズの中心厚、ｎ5は第５レンズの屈折率とする。
ｆ2×（ν5−ν4）／｛ＲA・（Ｂｆ＋Ｄ5／ｎ5）｝≧１０ ……（２）
この条件式の下限はさらに以下の値であることが倍率色収差補正の点でより好ましい。
ｆ2×（ν5−ν4）／｛ＲA・（Ｂｆ＋Ｄ5／ｎ5）｝≧１７ ……（２Ａ）
The endoscope objective lens preferably satisfies the following conditional expression with respect to the cemented lens L45. Where ν 4 is the Abbe number of the fourth lens L4, ν 5 is the Abbe number of the fifth lens L5, R A is the radius of curvature of the joint surface between the fourth lens and the fifth lens, and D 5 is the center of the fifth lens. The thickness, n 5 is the refractive index of the fifth lens.
f 2 × (ν 5 −ν 4 ) / {R A · (Bf + D 5 / n 5 )} ≧ 10 (2)
The lower limit of this conditional expression is more preferably the following value from the viewpoint of correcting chromatic aberration of magnification.
f 2 × (ν 5 −ν 4 ) / {R A · (Bf + D 5 / n 5 )} ≧ 17 (2A)
次に、以上のように構成された内視鏡用対物レンズの作用および効果を説明する。
この内視鏡用対物レンズでは、全系のバックフォーカスＢｆを全系の合成焦点距離ｆの２倍よりも長くした４群５枚のレンズ構成において、明るさ絞りＳｔから離れた場所で最も像面側に倍率色収差補正を担う光学部材として接合レンズを配置し、かつ、各レンズの硝材を適切なものとすることで、像面側に光路変換プリズムＧＰを挿入配置することが可能な十分な長さのバックフォーカスを確保しつつ、倍率色収差を良好に補正している。
Next, operations and effects of the endoscope objective lens configured as described above will be described.
In this endoscope objective lens, in the four-group five-lens configuration in which the back focal length Bf of the entire system is longer than twice the combined focal length f of the entire system, the most image is obtained at a place far from the aperture stop St. By arranging a cemented lens as an optical member for correcting chromatic aberration of magnification on the surface side and using an appropriate glass material for each lens, the optical path conversion prism GP can be inserted and disposed on the image surface side. The lateral chromatic aberration is satisfactorily corrected while ensuring a long back focus.
通常、色収差の補正が不十分な結像レンズにおいては、短波長における焦点距離が長波長の焦点距離よりも短いので、軸上色収差と倍率色収差共に短波長が基準波長に比べマイナス（アンダー）となる。ここで倍率色収差のアンダーを補正する場合、明るさ絞りＳｔより後方では、正レンズのアッベ数は大きく、負レンズのアッベ数は小さくすると良い。逆に明るさ絞りＳｔより前方では、正レンズのアッベ数は小さく、負レンズのアッベ数は大きくすると良い。上記条件式（１）を満足することで、明るさ絞りＳｔに対して物体側にある正の第２レンズＬ２と明るさ絞りＳｔに対して像面側にありかつ最も像面に近い位置にある負の第５レンズＬ５とのアッベ数を小さく抑えることができ、倍率色収差の補正をし易くなる。 Normally, in an imaging lens with insufficient correction of chromatic aberration, the focal length at the short wavelength is shorter than the focal length at the long wavelength, so both the longitudinal chromatic aberration and the lateral chromatic aberration are smaller (under) than the reference wavelength. Become. Here, when correcting under-magnification chromatic aberration, it is preferable that the Abbe number of the positive lens is large and the Abbe number of the negative lens is small behind the aperture stop St. On the contrary, in front of the aperture stop St, it is preferable that the Abbe number of the positive lens is small and the Abbe number of the negative lens is large. By satisfying the conditional expression (1), the positive second lens L2 on the object side with respect to the aperture stop St and the position on the image plane side with respect to the aperture stop St and closest to the image plane. The Abbe number with a certain negative fifth lens L5 can be kept small, and it becomes easy to correct lateral chromatic aberration.
条件式（２）は、色収差補正を担う光学部材としての接合レンズＬ４５における接合面の倍率色収差に対する補正の度合いを示している。条件式（２）は、接合レンズＬ４５を構成する第４レンズＬ４と第５レンズＬ５とのアッベ数の差（ν5−ν4）を、全系の合成焦点距離ｆで規格化した接合レンズＬ４５の接合面の曲率半径ＲAと全系のバックフォーカスＢｆに第５レンズＬ５の空気換算長Ｄ5／ｎ5を加えた値（Ｂｆ＋Ｄ5／ｎ5）とで割ったものである。条件式（２）は、第４レンズＬ４と第５レンズＬ５とのアッベ数差（ν5−ν4）が大きく、また、接合面の曲率半径ＲAが小さく、接合面が結像位置に短いほど倍率色収差の補正に有利なことを示す。 Conditional expression (2) indicates the degree of correction with respect to lateral chromatic aberration of the cemented surface in the cemented lens L45 as an optical member responsible for chromatic aberration correction. Conditional expression (2) is a cemented lens in which the Abbe number difference (ν 5 −ν 4 ) between the fourth lens L4 and the fifth lens L5 constituting the cemented lens L45 is normalized by the total focal length f of the entire system. the radius of curvature R a and the back focus Bf of the whole system of the joint surface of the L45 is obtained by dividing out the equivalent air length D 5 / n 5 a value obtained by adding the fifth lens L5 (Bf + D 5 / n 5). Conditional expression (2) shows that the Abbe number difference (ν 5 −ν 4 ) between the fourth lens L4 and the fifth lens L5 is large, the radius of curvature R A of the cemented surface is small, and the cemented surface is at the imaging position. The shorter the value, the better the correction of chromatic aberration of magnification.
以上説明したように、本実施の形態に係る内視鏡用対物レンズによれば、全系のバックフォーカスＢｆが全系の合成焦点距離ｆの２倍よりも長い内視鏡用対物レンズにおいて、最も像面側に倍率色収差補正を担う光学部材として接合レンズＬ４５を配置し、さらに条件式（１）を満足して、明るさ絞りＳｔに対して物体側にある正の第２レンズＬ２と明るさ絞りＳｔに対して像面側にありかつ最も像面に近い位置にある負の第５レンズＬ５とのアッベ数を小さく抑えるようにしたので、像面側に光路変換プリズムＧＰを挿入配置することが可能な十分な長さのバックフォーカスを確保しつつ、倍率色収差を良好に補正することができる。 As described above, according to the endoscope objective lens according to the present embodiment, in the endoscope objective lens, the back focus Bf of the entire system is longer than twice the combined focal length f of the entire system. The cemented lens L45 is disposed as an optical member for correcting the chromatic aberration of magnification on the most image side, and further satisfies the conditional expression (1), and the positive second lens L2 on the object side with respect to the aperture stop St and the brightness. Since the Abbe number with the negative fifth lens L5 located closest to the image plane and closest to the image plane with respect to the aperture stop St is suppressed, the optical path conversion prism GP is inserted and disposed on the image plane side. Therefore, it is possible to satisfactorily correct lateral chromatic aberration while ensuring a sufficiently long back focus.
次に、本実施の形態に係る内視鏡用対物レンズの具体的な数値実施例について説明する。以下では、第１〜第６の数値実施例をまとめて説明する。 Next, specific numerical examples of the endoscope objective lens according to the present embodiment will be described. Hereinafter, the first to sixth numerical examples will be described together.
図７は実施例１に係る内視鏡用対物レンズの基本的なレンズデータを示している。この実施例１に係る内視鏡用対物レンズの基本的なレンズ構成は、既に図１を参照して説明したとおりである。図７に示したレンズデータにおける面番号Ｓｉの欄には、最も物体側の構成要素の面を１番目として、像側に向かうに従い順次増加するようにして符号を付したｉ番目（ｉ＝１〜１２）の面の番号を示している。曲率半径Ｒｉの欄には、図１において付した符号Ｒｉに対応させて、物体側からｉ番目の面の曲率半径の値（ｍｍ）を示す。面間隔Ｄｉの欄についても、同様に物体側からｉ番目の面Ｓｉとｉ＋１番目の面Ｓｉ＋１との光軸上の間隔（ｍｍ）を示す。ｎｄｊは、隣り合うレンズ面間のｄ線（波長５８７．６ｎｍ）に対する屈折率の値を示す。νｄｊの欄には、物体側からｊ番目（ｊ＝１〜６）の光学要素のｄ線に対するアッベ数の値を示す。なお、曲率半径Ｒｉと面間隔Ｄｉの数値は、全系の合成焦点距離ｆが１．０ｍｍとなるように規格化してある。 FIG. 7 shows basic lens data of the endoscope objective lens according to the first embodiment. The basic lens configuration of the endoscope objective lens according to Example 1 is as already described with reference to FIG. In the field of the surface number Si in the lens data shown in FIG. 7, the surface of the component closest to the object side is the first, and the i-th (i = 1) is assigned so as to increase sequentially toward the image side. To 12). In the column of the curvature radius Ri, the value (mm) of the curvature radius of the i-th surface from the object side is shown in correspondence with the reference symbol Ri in FIG. Similarly, the column of the surface interval Di indicates the interval (mm) on the optical axis between the i-th surface Si and the i + 1-th surface Si + 1 from the object side. ndj represents the value of the refractive index for the d-line (wavelength 587.6 nm) between adjacent lens surfaces. In the column νdj, the Abbe number value for the d-line of the j-th (j = 1 to 6) optical element from the object side is shown. The numerical values of the curvature radius Ri and the surface interval Di are standardized so that the total focal length f of the entire system is 1.0 mm.
以上の実施例１に係る内視鏡用対物レンズと同様にして、実施例２に係る内視鏡用対物レンズの基本的なレンズデータを図８に示す。実施例２に係る内視鏡用対物レンズの基本的なレンズ構成は、既に図２を参照して説明したとおりである。また同様にして、実施例３ないし実施例６に係る内視鏡用対物レンズの基本的なレンズデータをそれぞれ、図９〜図１２に示す。実施例３ないし実施例６に係る内視鏡用対物レンズの基本的なレンズ構成はそれぞれ、既に図３〜図６を参照して説明したとおりである。なお、実施例２ないし実施例６についても、実施例１と同様に、曲率半径Ｒｉと面間隔Ｄｉの数値は、全系の合成焦点距離ｆが１．０ｍｍとなるように規格化してある。 FIG. 8 shows basic lens data of the endoscope objective lens according to the second embodiment in the same manner as the endoscope objective lens according to the first embodiment. The basic lens configuration of the endoscope objective lens according to Example 2 is as already described with reference to FIG. Similarly, basic lens data of the endoscope objective lens according to Examples 3 to 6 are shown in FIGS. 9 to 12, respectively. The basic lens configurations of the endoscope objective lenses according to the third to sixth embodiments are as already described with reference to FIGS. In Examples 2 to 6, as in Example 1, the numerical values of the curvature radius Ri and the surface distance Di are standardized so that the total focal length f of the entire system is 1.0 mm.
図１３には、その他の諸データとして、各実施例の対物レンズにおけるイメージサイズ、被写体距離、画角、バックフォーカスＢｆ、最外画角での倍率色収差の値（Ｆ線−Ｃ線）および上記条件式の値を示す。なお、Ｃ線は波長６５６．２７ｎｍ、Ｆ線は波長４８６．１３ｎｍである。図１３から分かるように、各実施例の値が、条件式（１），（２）の数値範囲内となっている。また各実施例について全系のバックフォーカスＢｆが全系の合成焦点距離ｆの２倍よりも長くなっている。なお、各条件式におけるアッベ数νおよび屈折率ｎはｄ線を基準波長とした値で計算している。
ここで、実施例１、実施例２、実施例４および実施例６においては、条件式（１）のより好ましい値である条件式（１Ａ）をも満足している。また、実施例１、実施例２、実施例３、実施例５および実施例６においては、条件式（２）のより好ましい値である条件式（２Ａ）をも満足している。
In FIG. 13, as other data, the image size, subject distance, field angle, back focus Bf, magnification chromatic aberration value at the outermost field angle (F line-C line) and the above-described values are shown as other data. Indicates the value of the conditional expression. The C line has a wavelength of 656.27 nm, and the F line has a wavelength of 486.13 nm. As can be seen from FIG. 13, the values of the respective examples are within the numerical ranges of the conditional expressions (1) and (2). In each embodiment, the back focal length Bf of the entire system is longer than twice the combined focal length f of the entire system. Note that the Abbe number ν and the refractive index n in each conditional expression are calculated with values using the d-line as a reference wavelength.
Here, in Example 1, Example 2, Example 4, and Example 6, the conditional expression (1A) that is a more preferable value of the conditional expression (1) is also satisfied. In Example 1, Example 2, Example 3, Example 5, and Example 6, the conditional expression (2A), which is a more preferable value of the conditional expression (2), is also satisfied.
図１３には、本実施の形態に係る内視鏡用対物レンズに対する比較例の内視鏡用対物レンズについての値も示す。比較例の内視鏡用対物レンズは、条件式（２）を除く他の条件式の値から外れ、また倍率色収差の値が各実施例の値に比べて大きくなっている。ここで、比較例の内視鏡用対物レンズの構成を図２０に示す。また、比較例の内視鏡用対物レンズの基本的なレンズデータを図２１に示す。符号は本実施の形態に係る内視鏡用対物レンズに対応する部分に同一の記号を付している。この比較例の内視鏡用対物レンズにおいて、光路変換プリズムＧＰと結像位置Ｐとの間にはカバーガラスＧＣが配置されている。この比較例は、上記特許文献３（特開２００４−６１７６３号公報）に数値実施例として記載されているものである。ただし、曲率半径Ｒｉと面間隔Ｄｉの数値は、全系の合成焦点距離ｆが１．０ｍｍとなるように規格化してある。 FIG. 13 also shows values for the endoscope objective lens of the comparative example with respect to the endoscope objective lens according to the present embodiment. The endoscope objective lens of the comparative example deviates from the values of the other conditional expressions except the conditional expression (2), and the value of the lateral chromatic aberration is larger than the values of the respective examples. Here, FIG. 20 shows a configuration of the endoscope objective lens of the comparative example. FIG. 21 shows basic lens data of the endoscope objective lens of the comparative example. Reference numerals are assigned to the portions corresponding to the endoscope objective lens according to the present embodiment. In the endoscope objective lens of this comparative example, a cover glass GC is disposed between the optical path conversion prism GP and the imaging position P. This comparative example is described as a numerical example in Patent Document 3 (Japanese Patent Laid-Open No. 2004-61763). However, the numerical values of the curvature radius Ri and the surface interval Di are normalized so that the total focal length f of the entire system is 1.0 mm.
図１４（Ａ）〜図１４（Ｄ）はそれぞれ、実施例１に係る内視鏡用対物レンズにおける球面収差、非点収差、ディストーション（歪曲収差）、および倍率色収差を示している。各収差図には、ｄ線を基準波長とした収差を示す。球面収差は、Ｃ線およびＦ線についての収差も示す。倍率色収差はＣ線およびＦ線について示す。ＦＮＯ．はＦ値、ωは半画角を示す。 FIGS. 14A to 14D show spherical aberration, astigmatism, distortion (distortion aberration), and lateral chromatic aberration in the endoscope objective lens according to Example 1, respectively. Each aberration diagram shows an aberration with the d-line as a reference wavelength. Spherical aberration also indicates aberration for C-line and F-line. Lateral chromatic aberration is shown for the C and F lines. FNO. Indicates an F value, and ω indicates a half angle of view.
同様にして、実施例２に係る内視鏡用対物レンズについての諸収差を図１５（Ａ）〜図１５（Ｄ）に、実施例３に係る内視鏡用対物レンズについての諸収差を図１６（Ａ）〜図１６（Ｄ）に、実施例４に係る内視鏡用対物レンズについての諸収差を図１７（Ａ）〜図１７（Ｄ）に、実施例５に係る内視鏡用対物レンズについての諸収差を図１８（Ａ）〜図１８（Ｄ）に、実施例６に係る内視鏡用対物レンズについての諸収差を図１９（Ａ）〜図１９（Ｄ）に示す。さらに、図２０および図２１に示した比較例の内視鏡用対物レンズについての諸収差を図２２（Ａ）〜図２２（Ｄ）に示す。 Similarly, various aberrations for the endoscope objective lens according to Example 2 are shown in FIGS. 15A to 15D, and various aberrations for the endoscope objective lens according to Example 3 are shown. 16 (A) to 16 (D) show various aberrations of the endoscope objective lens according to Example 4, and FIGS. 17 (A) to 17 (D) show the various aberrations for the endoscope according to Example 5. Various aberrations for the objective lens are shown in FIGS. 18A to 18D, and various aberrations for the endoscope objective lens according to Example 6 are shown in FIGS. 19A to 19D. Further, various aberrations regarding the endoscope objective lens of the comparative example shown in FIGS. 20 and 21 are shown in FIGS. 22 (A) to 22 (D).
以上の各数値データおよび各収差図から分かるように、各実施例について、比較例の内視鏡用対物レンズに比べて特に倍率色収差が良好に補正された内視鏡用対物レンズが実現できている。 As can be seen from the above numerical data and aberration diagrams, in each example, an endoscope objective lens in which the lateral chromatic aberration was corrected well compared to the endoscope objective lens of the comparative example could be realized. Yes.
なお、本発明は、上記実施の形態および各実施例に限定されず種々の変形実施が可能である。例えば、各レンズ成分の曲率半径、面間隔および屈折率の値などは、上記各数値実施例で示した値に限定されず、他の値をとり得る。 In addition, this invention is not limited to the said embodiment and each Example, A various deformation | transformation implementation is possible. For example, the radius of curvature, the surface interval, and the refractive index of each lens component are not limited to the values shown in the above numerical examples, and may take other values.
ＧＰ…光路変換プリズム、Ｌ１…第１レンズ、Ｌ２…第２レンズ、Ｌ３…第３レンズ、Ｌ４…第４レンズ、Ｌ５…第５レンズ、Ｌ４５…接合レンズ、Ｓｔ…明るさ絞り、Ｒｉ…物体側から第ｉ番目のレンズ面の曲率半径、Ｄｉ…物体側から第ｉ番目と第ｉ＋１番目のレンズ面との面間隔、Ｚ１…光軸。 GP ... optical path conversion prism, L1 ... first lens, L2 ... second lens, L3 ... third lens, L4 ... fourth lens, L5 ... fifth lens, L45 ... junction lens, St ... brightness stop, Ri ... object Radius of curvature of the i-th lens surface from the side, Di... The surface interval between the i-th and i + 1-th lens surfaces from the object side, Z1.
Claims (2)
前記第２レンズと前記第３レンズとの間に明るさ絞りが配置され、全系のバックフォーカスが全系の合成焦点距離の２倍よりも長く、かつ、下記条件式を満足するように構成されている
（ν2＋ν5）＜４５ ……（１）
ことを特徴とする内視鏡用対物レンズ。
ただし、
ν2：第２レンズのアッベ数
ν5：第５レンズのアッベ数
とする。 In order from the object side, a negative first lens whose surface on the image surface side is a concave surface, and a positive surface whose surface on the image surface side is a plane or a surface having a larger absolute value of the radius of curvature than the surface on the object side A second lens, a positive third lens whose surface on the object side is a plane or a surface having a larger absolute value of the radius of curvature than the surface on the image plane side, and the surface on the object side is a plane or surface on the image plane side And a cemented lens having a positive refractive power as a whole, which is composed of a positive fourth lens and a negative meniscus fifth lens whose surface has a large absolute value of the radius of curvature.
An aperture stop is disposed between the second lens and the third lens, and the back focal length of the entire system is longer than twice the combined focal length of the entire system, and satisfies the following conditional expression: (Ν 2 + ν 5 ) <45 (1)
An objective lens for an endoscope.
However,
ν 2 : Abbe number of the second lens ν 5 : Abbe number of the fifth lens.
ｆ2×（ν5−ν4）／｛ＲA・（Ｂｆ＋Ｄ5／ｎ5）｝≧１０ ……（２）
ことを特徴とする請求項１に記載の内視鏡用対物レンズ。
ただし、
ｆ：全系の合成焦点距離
Ｂｆ：全系のバックフォーカス
ν4：第４レンズのアッベ数
ν5：第５レンズのアッベ数
ＲA：第４レンズと第５レンズとの接合面の曲率半径
Ｄ5：第５レンズの中心厚
ｎ5：第５レンズの屈折率
とする。 Furthermore, the following conditional expression is satisfied: f 2 × (ν 5 −ν 4 ) / {R A · (Bf + D 5 / n 5 )} ≧ 10 (2)
The endoscope objective lens according to claim 1.
However,
f: Total focal length of the entire system Bf: Back focus of the entire system ν 4 : Abbe number of the fourth lens ν 5 : Abbe number of the fifth lens R A : Radius of curvature of the cemented surface between the fourth lens and the fifth lens D 5 : Center thickness of the fifth lens n 5 : Refractive index of the fifth lens.
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