JPS6236692B2 - - Google Patents
Info
- Publication number
- JPS6236692B2 JPS6236692B2 JP57216329A JP21632982A JPS6236692B2 JP S6236692 B2 JPS6236692 B2 JP S6236692B2 JP 57216329 A JP57216329 A JP 57216329A JP 21632982 A JP21632982 A JP 21632982A JP S6236692 B2 JPS6236692 B2 JP S6236692B2
- Authority
- JP
- Japan
- Prior art keywords
- light
- observation
- corneal
- microscope according
- dichroic mirror
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
- 238000005286 illumination Methods 0.000 claims description 10
- 230000003287 optical effect Effects 0.000 claims description 7
- 230000005540 biological transmission Effects 0.000 claims description 3
- 230000001105 regulatory effect Effects 0.000 claims 4
- 210000004087 cornea Anatomy 0.000 description 10
- 238000005259 measurement Methods 0.000 description 8
- 238000003384 imaging method Methods 0.000 description 5
- 238000001356 surgical procedure Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 2
- 230000000903 blocking effect Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 229910052736 halogen Inorganic materials 0.000 description 1
- 150000002367 halogens Chemical class 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 229910052724 xenon Inorganic materials 0.000 description 1
- FHNFHKCVQCLJFQ-UHFFFAOYSA-N xenon atom Chemical compound [Xe] FHNFHKCVQCLJFQ-UHFFFAOYSA-N 0.000 description 1
Landscapes
- Microscoopes, Condenser (AREA)
- Eye Examination Apparatus (AREA)
Description
【発明の詳細な説明】
本発明は医科手術用の顕微鏡に関し、特に自動
的に角膜の曲率測定を行う測定装置を備えた顕微
鏡に関する。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a medical and surgical microscope, and more particularly to a microscope equipped with a measuring device that automatically measures corneal curvature.
眼科の手術は顕微鏡を覗きながら行うことが多
いが、角膜手術で患部の縫合を行う際には、角膜
の曲率半径を測定しながらその測定値に合わせて
縫合の程度を手かげんしている。そしてこの様な
用途のための顕微鏡には手動のケラトメータが組
込まれているが、手術を行う一方でケラトメータ
の操作をするのは著しく煩雑である。 Eye surgery is often performed while looking through a microscope, but when suturing the affected area during corneal surgery, the radius of curvature of the cornea is measured and the degree of suturing is adjusted accordingly. Although a manual keratometer is built into a microscope for such use, it is extremely troublesome to operate the keratometer while performing surgery.
本発明の目的は、角膜の曲率を自動的に測定し
得る装置を備える顕微鏡を提供することにある。
但し自動測定をするための光電検出手段に、患部
観察のための観察光が入射した場合、正確な測定
を妨げる。この様な難点を解決する一方として
は、測定時と観察時とを時間分割する手法が挙げ
られるが、本発明は観察の連続性を保ちつつ前記
難点を除去することを副目的とする。 An object of the present invention is to provide a microscope equipped with a device that can automatically measure the curvature of the cornea.
However, if the observation light for observing the affected area is incident on the photoelectric detection means for automatic measurement, accurate measurement will be hindered. One way to solve these difficulties is to time-divide the time of measurement and observation, but a secondary objective of the present invention is to eliminate the above-mentioned difficulties while maintaining continuity of observation.
以下、図面に従つて本発明の実施例を説明す
る。第１図でＥは被検眼、Ｃはその角膜である。
１は照明光源で、例えばハロゲン球を使用する。
２は波長カツトフイルターで、近赤外光より長波
長側の光を遮断し、短波長側の光を透過させる作
用を持ち、これにより光源１を発した光の内、近
赤外光を除去することができる。３はコリメータ
レンズで、被検部を一様に照明するのに役立つ。
以上の光源１、波長カツトフイルター２、コリメ
ータレンズ３が順値されて観察照明系を構成す
る。 Embodiments of the present invention will be described below with reference to the drawings. In FIG. 1, E is the eye to be examined and C is its cornea.
Reference numeral 1 denotes an illumination light source, which uses a halogen bulb, for example.
2 is a wavelength cut filter, which has the effect of blocking light with longer wavelengths than near-infrared light and transmitting light with shorter wavelengths, thereby removing near-infrared light from the light emitted from light source 1. can do. 3 is a collimator lens, which is useful for uniformly illuminating the area to be examined.
The above-mentioned light source 1, wavelength cut filter 2, and collimator lens 3 are combined to form an observation illumination system.
次に５は大口径の対物レンズ、６と７はリレー
レンズで、リレーレンズ６と７の光軸は平行に配
される。８と９は双眼視のための接眼レンズで、
リレーレンズ６と７による像をそれぞれ目視する
のに役立つ。以上の対物レンズ５、リレーレンズ
６と７、接眼レンズ８と９は角膜観察系を構成す
る。 Next, 5 is a large-diameter objective lens, and 6 and 7 are relay lenses, and the optical axes of the relay lenses 6 and 7 are arranged in parallel. 8 and 9 are eyepieces for binocular vision.
This is useful for visually viewing the images formed by the relay lenses 6 and 7, respectively. The objective lens 5, relay lenses 6 and 7, and eyepiece lenses 8 and 9 constitute a corneal observation system.
更に１０はダイクロイツクミラーで、近赤外光
より長波長側の光を反射させ、短波長側の光を透
過させる作用を持ち、これにより近赤外光を選択
することができる。ダイクロイツクミラー１０は
角膜観察系の一方の光路に斜設される。１１は結
像レンズ。１２は波長透過フイルターで、近赤外
光を透過させる作用を持つ。但し、ダイクロイツ
クミラーの波長分離性能が高い場合はフイルター
１２を省略することができ、あるいはダイクロイ
ツクミラーの替りに半透鏡を使用することが可能
でである。１３は二次元撮像用の光電変換器で、
例えばCCD（Charge Coupled Device）の様な
固体撮像素子を使用する。以上の対物レンズ５、
リレーレンズ７、ダイクロイツクミラー１０、結
像レンズ１１、フイルター１２、光電変換器１３
は角膜曲率測定装置の受光部を構成する。また１
はリング状光源で、環態のキセノン閃光放電管を
用い、測定装置の照明系を構成する。 Furthermore, 10 is a dichroic mirror which has the function of reflecting light on the longer wavelength side than near-infrared light and transmitting light on the shorter wavelength side, so that near-infrared light can be selected. A dichroic mirror 10 is installed obliquely on one optical path of the corneal observation system. 11 is an imaging lens. Reference numeral 12 denotes a wavelength transmission filter, which has the function of transmitting near-infrared light. However, if the dichroic mirror has high wavelength separation performance, the filter 12 can be omitted, or a semi-transparent mirror can be used instead of the dichroic mirror. 13 is a photoelectric converter for two-dimensional imaging;
For example, a solid-state image sensor such as a CCD (Charge Coupled Device) is used. The above objective lens 5,
Relay lens 7, dichroic mirror 10, imaging lens 11, filter 12, photoelectric converter 13
constitutes the light receiving section of the corneal curvature measuring device. Also 1
is a ring-shaped light source, which uses an annular xenon flash discharge tube to constitute the illumination system of the measuring device.
ここでまず角膜曲率測定装置の作用を説明す
る。 First, the operation of the corneal curvature measuring device will be explained.
第１図でリング状光源１４は被検眼Ｅの角膜Ｃ
により反射像１４（虚像）を形成する。この反射
像１４は投影系５，７，１０，１１により光電変
換器１３上へ投影像１４″（第２図）として結像
される。投影指標としてのリング状光源１４とし
ては、円周上に複数個の光源が設けられたもので
あつてもよいし、投影指標として光路中にリング
状スリツトを設けてもよい。ここで角膜Ｃは一般
にトーリツク面とみなされるため、リング状光源
１４が真円であつても角膜反射像１４′は楕円と
なる。またこれより投影系による投影像１４″は
楕円となる。 In FIG. 1, the ring-shaped light source 14 is the cornea C of the eye E to be examined.
A reflected image 14 (virtual image) is formed. This reflected image 14 is formed as a projected image 14'' (FIG. 2) on the photoelectric converter 13 by the projection systems 5, 7, 10, 11. A plurality of light sources may be provided in the optical path, or a ring-shaped slit may be provided in the optical path as a projection index.Here, since the cornea C is generally regarded as a toric surface, the ring-shaped light source 14 Even if it is a perfect circle, the corneal reflection image 14' becomes an ellipse. Also, from this, the projected image 14'' by the projection system becomes an ellipse.
第２図の光電変換器１３に投影された投影像１
４″と、これを横切る適当な間隔の３本の走査線
１５，１６，１７により投影像１４″との交点１
５′，１５″，１６′，１６″，１７′，１７″が求ま
る。これら交点のうち、５点の座標より投影像１
４″の楕円形状を求めることより被検眼の角膜曲
率を算出する。 Projected image 1 projected onto the photoelectric converter 13 in FIG.
4'' and the projected image 14'' by three scanning lines 15, 16, 17 at appropriate intervals crossing it.
5', 15'', 16', 16'', 17', 17'' are determined. Projection image 1 is calculated from the coordinates of 5 points among these intersection points.
The corneal curvature of the eye to be examined is calculated by determining the elliptical shape of 4''.
一般に楕円の方程式は任意の座標ｘ，ｙに対
し、
dx2＋by2＋2cxy＋dx＋ey＋１＝０
と書き表わせる。ここでａ〜ｅの５つが未知数で
ある。 Generally, the equation of an ellipse can be written as dx 2 +by 2 +2cxy+dx+ey+1=0 for arbitrary coordinates x and y. Here, five of a to e are unknown quantities.
これより、平面上の楕円の形状は５点の座標よ
り決定され、最小３本の走査線を使えばよいこと
が理解される。 From this, it can be understood that the shape of an ellipse on a plane is determined by the coordinates of five points, and that it is sufficient to use a minimum of three scanning lines.
第１図へ戻つて、光源１を点灯すれば、光源１
を発した光の内、可視波長域の光はフイルター２
を透過し、レンズ３を介して角膜Ｃを一様に照明
する。角膜Ｃからの散乱反射光は対物レンズ５で
収斂作用を受け、更に各リレーレンズ６と７で
夫々結像される。これらの像はパララツクスを持
ち、各像は各接眼レンズ８，９を通して観察され
る。適当な時点で、レンズ状光源１４は瞬時点灯
し、そこから来る光は角膜Ｃを照明し、角膜Ｃで
反射された光は対物レンズ５とリレーレンズ７に
収斂作用を受け、その後ダイクロイツクミラー１
０で反射する際に近赤外より長波長側の光が反射
し、結像レンズ１１により光電変換器１３上にリ
ング状の虚光源像１４′を結像する。そして角膜
Ｃで反射した光の内、近赤外より短波長側の可視
光はダイクロイツクミラー１０を透過するので光
電変換器１３に達することはなく、また仮にダイ
クロイツクミラーで可視光が多少反射したとして
もフイルター１２で遮断されるから、光電変換時
の雑音になることはない。なお、光電変換器１３
で検出された情報に基づいて演算された角膜曲率
に関する値（長軸、短軸方向の曲率と軸の角度）
は装置の外部に表示しても良いし、あるいはリレ
ーレンズ６による結像面上の周縁に接眼レンズ８
へ向けて表示しても良い。 Returning to Figure 1, if light source 1 is turned on, light source 1
Of the light emitted, the light in the visible wavelength range is passed through filter 2.
is transmitted through the lens 3 to uniformly illuminate the cornea C. The scattered reflected light from the cornea C is converged by the objective lens 5, and is further imaged by the relay lenses 6 and 7, respectively. These images have parallax, and each image is observed through each eyepiece 8,9. At an appropriate point in time, the lenticular light source 14 is turned on momentarily, the light coming from it illuminates the cornea C, the light reflected by the cornea C is converged by the objective lens 5 and the relay lens 7, and then passes through the dichroic mirror. 1
When reflected at zero, light with a longer wavelength than near infrared is reflected, and a ring-shaped virtual light source image 14' is formed on the photoelectric converter 13 by the imaging lens 11. Of the light reflected by the cornea C, visible light with wavelengths shorter than near infrared passes through the dichroic mirror 10, so it does not reach the photoelectric converter 13. Also, even if some visible light is reflected by the dichroic mirror, Even if it does, it is blocked by the filter 12, so it does not become noise during photoelectric conversion. Note that the photoelectric converter 13
Values related to corneal curvature calculated based on information detected by (major axis, short axis curvature and axis angle)
may be displayed on the outside of the device, or an eyepiece 8 may be displayed on the periphery of the image forming plane formed by the relay lens 6.
It may also be displayed facing towards.
以上説明した本発明によれば、患部を顕微鏡観
察し得ると共に自動測定した角膜曲率の測定値を
確認できるもので、測定を手動で行う煩わしさか
ら解放される効果がある。また自動測定は雑音要
因から保護されているので、正確な測定値を得る
ことができる。 According to the present invention described above, the affected area can be observed under a microscope and the automatically measured value of the corneal curvature can be confirmed, which has the effect of freeing the user from the trouble of performing measurements manually. Automatic measurements are also protected from noise factors, ensuring accurate measurements.
一方、測定光源にストロボを使用すれば瞬時に
測定が実行され、あるいは光路中に配した光分割
器をダイクロイツクミラーにすれば観察視野が陰
る様なこともなくなる利点がある。 On the other hand, if a strobe is used as the measurement light source, the measurement can be carried out instantaneously, or if the light splitter placed in the optical path is a dichroic mirror, there is an advantage that the observation field of view will not be obscured.
第１図は本発明の実施例を示す光学断面図。第
２図は光電変換器とその上の投影像を示す。
図中、１は照明光源、２は近赤外カツトフイル
ター、３はコリメータレンズ、５は対物レンズ、
６と７はリレーレンズ、８と９は接眼レンズ、１
０はダイクロイツクミラー、１１は結像レンズ、
１２は近赤外透過、可視カツトフイルター、１３
は光電変換器である。
FIG. 1 is an optical sectional view showing an embodiment of the present invention. FIG. 2 shows a photoelectric converter and a projected image thereon. In the figure, 1 is an illumination light source, 2 is a near-infrared cut filter, 3 is a collimator lens, 5 is an objective lens,
6 and 7 are relay lenses, 8 and 9 are eyepiece lenses, 1
0 is a dichroic mirror, 11 is an imaging lens,
12 is a near-infrared transmission, visible cut filter, 13
is a photoelectric converter.
Claims (1)
明を行う観察照明系と、角膜曲率半径を測定する
ためで、光電検出器及び角膜照明系を具える測定
装置を設けると共に、観察照明系による照明光中
から所定の性質の光を除去するための除去手段
と、光電検出器へ入射する光を所定の性質の光の
みに規制する規制手段を設けたことを特徴とする
医科用顕微鏡。 ２ 所定の性質の光とは近赤外光である特許請求
の範囲第１項記載の医科用顕微鏡。 ３ 前記規制手段は近赤外光と可視光を反射と透
過で分離するダイクロイツクミラーである特許請
求の範囲第１項記載の医科用顕微鏡。 ４ 角膜照明系はリング状の閃光放電管を有する
特許請求の範囲第１項記載の医科用顕微鏡。 ５ 前記規制手段は近赤外光を反射し、可視光を
透過するダイクロイツクミラーで、観察系の光路
に斜設される特許請求の範囲第１項記載の医科用
顕微鏡。[Scope of Claims] 1. An observation system for observing an object to be examined, an observation illumination system for providing illumination for observation, and a measuring device for measuring the radius of corneal curvature, which includes a photoelectric detector and a corneal illumination system. In addition, a removing means for removing light of a predetermined property from the illumination light from the observation illumination system and a regulating means for regulating the light incident on the photoelectric detector to only light of a predetermined property are provided. Features of medical microscopes. 2. The medical microscope according to claim 1, wherein the light having a predetermined property is near-infrared light. 3. The medical microscope according to claim 1, wherein the regulating means is a dichroic mirror that separates near-infrared light and visible light by reflection and transmission. 4. The medical microscope according to claim 1, wherein the corneal illumination system includes a ring-shaped flash discharge tube. 5. The medical microscope according to claim 1, wherein the regulating means is a dichroic mirror that reflects near-infrared light and transmits visible light, and is installed obliquely in the optical path of the observation system.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57216329A JPS59105436A (en) | 1982-12-09 | 1982-12-09 | Medical endoscope |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57216329A JPS59105436A (en) | 1982-12-09 | 1982-12-09 | Medical endoscope |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS59105436A JPS59105436A (en) | 1984-06-18 |
| JPS6236692B2 true JPS6236692B2 (en) | 1987-08-08 |
Family
ID=16686822
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57216329A Granted JPS59105436A (en) | 1982-12-09 | 1982-12-09 | Medical endoscope |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS59105436A (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2010213995A (en) * | 2009-03-18 | 2010-09-30 | Olympus Medical Systems Corp | Surgical microscope |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6161119A (en) * | 1984-09-01 | 1986-03-28 | Canon Inc | Stereoscopic microscope |
| JPH0651023B2 (en) * | 1986-03-25 | 1994-07-06 | キヤノン株式会社 | Ophthalmic equipment |
| JP2835375B2 (en) * | 1993-11-12 | 1998-12-14 | キヤノン株式会社 | Optometry device |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5416890A (en) * | 1977-05-26 | 1979-02-07 | Terry Clifford Michael | Method of reforming cornea and surgical microscope |
| JPS5666235A (en) * | 1979-11-02 | 1981-06-04 | Canon Kk | Cornea meter |
| JPS56151929A (en) * | 1980-04-25 | 1981-11-25 | Canon Inc | Fundus camera |
| JPS5775634A (en) * | 1980-10-31 | 1982-05-12 | Olympus Optical Co | Eye bottom camera |
| JPS57158826A (en) * | 1981-03-27 | 1982-09-30 | Nippon Kogaku Kk <Nikon> | Automatic focusing device for stereoscopical microscope |
-
1982
- 1982-12-09 JP JP57216329A patent/JPS59105436A/en active Granted
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5416890A (en) * | 1977-05-26 | 1979-02-07 | Terry Clifford Michael | Method of reforming cornea and surgical microscope |
| JPS5666235A (en) * | 1979-11-02 | 1981-06-04 | Canon Kk | Cornea meter |
| JPS56151929A (en) * | 1980-04-25 | 1981-11-25 | Canon Inc | Fundus camera |
| JPS5775634A (en) * | 1980-10-31 | 1982-05-12 | Olympus Optical Co | Eye bottom camera |
| JPS57158826A (en) * | 1981-03-27 | 1982-09-30 | Nippon Kogaku Kk <Nikon> | Automatic focusing device for stereoscopical microscope |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2010213995A (en) * | 2009-03-18 | 2010-09-30 | Olympus Medical Systems Corp | Surgical microscope |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS59105436A (en) | 1984-06-18 |
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