JP7317633B2 - ophthalmic equipment - Google Patents

Description

The present invention relates to an ophthalmologic apparatus that projects a measurement pattern onto the cornea of an eye to be inspected and photographs the cornea onto which the measurement pattern is projected.

In cataract surgery, an opacified crystalline lens is removed from an eye to be examined (patient's eye), which is the eye of a subject (patient), and an intraocular lens (IOL) is inserted into the eye to be examined. As this intraocular lens, a toric IOL capable of correcting astigmatism is known.

In order to exhibit the correction effect of the toric IOL, it is necessary to match the direction of the strong principal meridian of the cornea of the subject's eye with the direction of the weak principal meridian of the toric IOL as much as possible. Therefore, in cataract surgery using a toric IOL, measurement of the astigmatism axis direction (also referred to as the astigmatism axis angle) of the subject's eye is extremely important. Therefore, cataract surgery using a toric IOL is performed using a surgical microscope capable of measuring the direction of the astigmatic axis of the subject's eye and notifying the operator of this.

Patent Literatures 1 and 2 describe surgical microscopes that include a keratizing light source having a plurality of bright points (light sources) arranged in a ring shape and an imaging optical system having an imaging device. This surgical microscope projects an intermittent ring pattern (measurement pattern) onto the cornea of the subject's eye from a keratling light source, and photographs the cornea on which this ring pattern is projected with an imaging optical system. . Then, the surgical microscope calculates the astigmatism axis direction (astigmatism information) of the subject's eye based on the photographed image of the cornea taken by the photographing optical system, and blinks the bright spot corresponding to this astigmatism axis direction. , the operator is notified of the astigmatism axis direction of the cornea.

JP 2012-152454 A JP 2013-27536 A

When projecting the ring pattern from the keratling light source of the surgical microscope onto the cornea of the subject's eye, the distance between the subject's eye and the keratling light source is fixed at a predetermined reference value. This reference value is predetermined so that the size (diameter) of the ring pattern on the cornea is approximately 3φ (mm) in accordance with the general pupil diameter of the subject's eye.

However, the pupil diameter of the subject's eye differs from subject to subject, and in some cases the pupil diameter of the subject's eye differs greatly from the general pupil diameter described above. In this case, even if the distance between the eye to be inspected and the keratling light source is adjusted to the above reference value, the ring pattern projected from the keratling light source onto the cornea of the eye to be inspected is larger than the diameter of the pupil. There is a possibility that the astigmatism axis direction matching the diameter cannot be obtained.

SUMMARY OF THE INVENTION It is an object of the present invention to provide an ophthalmologic apparatus capable of acquiring astigmatism information of an eye to be examined that matches the pupil diameter of the eye to be examined.

An ophthalmologic apparatus for achieving the object of the present invention comprises: a projection light source for projecting a measurement pattern onto the cornea of an eye to be inspected; an imaging device for imaging the cornea on which the measurement pattern is projected by the projection light source; The light source is supported at a plurality of supporting positions along the projection axis of the projection light source and is predetermined based on a reference value of the distance between the subject's eye and the projection light source, and one or more positions different from the reference position. and a support for selectively supporting at a plurality of support positions including a cornea on which a measurement pattern is projected from a projection light source supported by the support at the change positions. to shoot.

According to this ophthalmologic apparatus, it is possible to project a measurement pattern that matches the pupil diameter of the eye to be inspected onto the cornea of the eye to be inspected, and to photograph the cornea of the eye to be inspected onto which the measurement pattern is projected.

In the ophthalmologic apparatus according to another aspect of the present invention, the projection axis and the optical axis of the imaging device are on the same straight line, the projection light source has an aperture through which the optical axis passes, the imaging device passes through the aperture, An image of the cornea on which the measurement pattern is projected is taken.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section is a linear guide provided in the photographing device and extending in a direction parallel to the optical axis to move the projection light source along the optical axis. A freely supporting guide and a fixing member selectively releasably fixing the projection light source to the guide at a plurality of supporting positions are provided. Thereby, the projection light source can be selectively supported at a plurality of support positions by the guide and the fixing member.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section is a linear guide provided in the photographing device and extending in a direction parallel to the optical axis to move the projection light source along the optical axis. A freely supporting guide and an actuator for moving the projection light source along the guide are provided. This makes it possible to more finely adjust the size of the measurement pattern projected from the projection light source onto the cornea of the eye to be inspected.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section can support the projection light source at a retracted position, which is a position closer to the imaging device than the reference position and the change position, as one of the plurality of support positions, A detection unit that detects whether or not the projection light source is supported by the support at the retracted position, and based on the detection result of the detection unit, the projection light source is turned off if the support supports the projection light source at the retracted position. and a light source control unit that turns on the projection light source when the projection light source is supported at a position different from the retracted position. As a result, the projection light source can be automatically switched on and off.

In the ophthalmologic apparatus according to another aspect of the present invention, the projection light source projects a continuous or intermittent ring pattern onto the cornea as the measurement pattern, and based on the captured image of the cornea captured by the imaging device, and an astigmatism information calculation unit for calculating astigmatism information of the subject's eye. Astigmatism information corresponding to the pupil diameter of the subject's eye is thereby obtained.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section sequentially supports the projection light source at two or more of the plurality of support positions, and the imaging device supports the projection light source at each of the two or more positions. The cornea on which the ring pattern is projected is photographed, and the astigmatism information calculation unit calculates astigmatism information for each of two or more positions based on the photographed images photographed for each of two or more positions by the photographing device. Astigmatism information at a plurality of locations of the subject's eye is thus obtained.

In the ophthalmologic apparatus according to another aspect of the present invention, the projection light source projects a continuous or intermittent ring pattern as the measurement pattern onto the cornea, and the support unit projects the projection light source to a plurality of support positions. The cornea on which the ring pattern is projected from the projection light source is photographed by the imaging device for each of the two or more positions, and the relative position of the changed position with respect to the reference position is acquired. corneal curvature calculation for calculating the corneal curvature of the eye to be inspected based on the relative position acquiring unit, the captured images of the cornea captured at each of two or more positions by the imaging device, and the relative positions acquired by the relative position acquiring unit and Thereby, the corneal curvature of the eye to be examined is obtained.

In an ophthalmic apparatus according to another aspect of the present invention, a projection light source projects a plurality of concentric ring patterns onto the cornea.

An ophthalmologic apparatus for achieving the object of the present invention comprises a projection light source for projecting a measurement pattern onto the cornea of an eye to be inspected, an observation optical system for observing the eye to be inspected, and comprising an objective lens, an eyepiece lens, and an eyepiece lens. and a relay optical system provided between the objective lens and the eyepiece lens, and the reflected light from the cornea on which the pattern for measurement is projected is guided to the eyepiece lens via the objective lens and the relay optical system. The optical system and the projection light source are supported at a plurality of supporting positions along the projection axis of the projection light source and are predetermined based on a reference value of the distance between the subject's eye and the projection light source; a support for selectively supporting at a plurality of support positions including: one or more different change positions; and a support for selectively supporting at a plurality of support positions, wherein the viewing optical system receives a measurement pattern from the projection light source supported at the change positions by the support. Reflected light from the cornea on which is projected is directed to the eyepiece.

In the ophthalmic apparatus according to another aspect of the present invention, the projection axis and the optical axis of the objective lens are on the same straight line, the projection light source has an aperture through which the optical axis passes, and the objective lens reflects light through the aperture. is incident.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section is a linear guide provided in the observation optical system and extending in a direction parallel to the optical axis, and the projection light source is guided along the optical axis. A movably supporting guide and a fixing member selectively releasably fixing the projection light source to the guide at a plurality of supporting positions are provided.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section is a linear guide provided in the observation optical system and extending in a direction parallel to the optical axis, and the projection light source is guided along the optical axis. A movably supporting guide and an actuator for moving the projection light source along the guide are provided.

In the ophthalmologic apparatus according to another aspect of the present invention, the support section can support the projection light source at a retracted position, which is a position closer to the observation optical system than the reference position and the change position, as one of the plurality of support positions. a detection unit for detecting whether or not the projection light source is supported by the support unit at the retracted position; a light source control unit that turns off the projection light source and turns on the projection light source when the projection light source is supported at a position different from the retracted position.

In the ophthalmologic apparatus according to another aspect of the present invention, the projection light source projects a continuous or intermittent ring pattern onto the cornea as the measurement pattern.

The present invention can acquire astigmatism information of an eye to be inspected that matches the pupil diameter of the eye to be inspected.

1 is a perspective view of a surgical microscope according to a first embodiment; FIG. It is a front view of a microscope main body. It is the bottom view which looked at the kerato ring light source from the downward side. FIG. 4 is a schematic diagram of the optical system inside the microscope main body when the microscope main body is viewed from the side; FIG. 2 is a schematic diagram of an optical system inside a microscope main body when the microscope main body is viewed from the operator's side; Fig. 10 is a perspective view of a keratling light source support; FIG. 4 is an explanatory diagram for explaining a reference position of a keratling light source; FIG. 10 is an explanatory diagram for explaining a first changed position of the keratling light source; FIG. 10 is an explanatory diagram for explaining a second changed position of the keratling light source; FIG. 4 is an explanatory diagram for explaining a retracted position of a keratling light source; FIG. 10 is an explanatory diagram for explaining the relationship between the support position of the keratling light source by a guide and the ring pattern projected from the keratling light source onto the cornea of the subject's eye E; It is a functional block diagram of the control device of the first embodiment. FIG. 10 is an explanatory diagram for explaining notification control in the direction of the astigmatic axis of the subject's eye by the notification control unit; 4 is a flow chart showing the flow of measurement of astigmatism information of an eye to be inspected and notification of astigmatism axis direction by the surgical microscope of the first embodiment. FIG. 10 is a functional block diagram of a control device for a surgical microscope according to a second embodiment; FIG. 4 is an explanatory diagram for explaining a first example of calculation of the corneal curvature of the subject's eye by the corneal curvature calculator; FIG. 10 is an explanatory diagram for explaining a second example of calculation of the corneal curvature of the subject's eye by the corneal curvature calculator; 10 is a flow chart showing the flow of calculation processing of the corneal curvature of the eye to be examined by the surgical microscope of the second embodiment; FIG. 11 is a bottom view of a modification of the keratling light source; It is explanatory drawing of the modification of a ring pattern. It is explanatory drawing of the modification of a kerato ring light source support part. FIG. 22 is a functional block diagram of the control device of the surgical microscope provided with the keratling light source support shown in FIG. 21; FIG. 4 is a block diagram of a surgical microscope provided with a modification of the microscope main body of the first embodiment;

[First embodiment]
<Configuration of surgical microscope>
FIG. 1 is a perspective view of a surgical microscope 10 (corresponding to the ophthalmologic apparatus of the present invention) of the first embodiment. As shown in FIG. 1, the surgical microscope 10 is used to observe the cornea of the eye E to be examined, measure the astigmatism axis direction, and measure the cornea of the eye E to be examined by the operator during cataract surgery on the eye E to be examined using a toric IOL. Notification (presentation) of the astigmatism axis direction is performed.

The surgical microscope 10 includes a leg 12 , a support 14 , a first arm 16 , a second arm 18 , a holder 20 , a footswitch 22 , a drive device 24 and a microscope main body 26 .

The leg portion 12 holds the support column 14 in a vertically parallel posture. The post 14 has its lower end fixed to the leg 12 and its upper end holding the first arm 16 .

One end of the first arm 16 is held by the upper end of the support 14 . Also, the other end of the first arm 16 is provided with a rotary drive shaft 24a constituted by a known electric actuator. The rotary drive shaft 24a holds the second arm 18 so as to be rotatable around a vertical axis parallel to the vertical direction and around a horizontal axis parallel to the horizontal direction.

One end of the second arm 18 is held by the first arm 16 via a rotary drive shaft 24a. Also, the other end of the second arm 18 is provided with a rotary drive shaft 24b constituted by a known electric actuator. The rotary drive shaft 24b holds the holder 20 rotatably around the vertical axis and around the horizontal axis. A holder 20 holds a microscope main body 26 .

The foot switch 22 accepts an input operation by the operator's foot and for changing the position and orientation of the microscope main body 26 .

The drive device 24 includes a rotary drive shaft 24a and a rotary drive shaft 24b. The driving device 24 vertically and horizontally moves or rotates the holder 20 and the microscope main body 26 according to the input operation to the foot switch 22 . As a result, the position and attitude of the microscope body 26 can be adjusted three-dimensionally by the driving device 24, so manual alignment of the microscope body 26 with respect to the eye E to be examined is possible.

FIG. 2 is a front view of the microscope main body 26. FIG. As shown in FIG. 2 and FIG. 1 already described, the microscope main body 26 corresponds to the photographing device of the present invention, and includes a lens barrel section 30, left and right eyepiece sections 32, and a photographing section 34 (see FIG. 1). (illustration is omitted here).

The lens barrel section 30 accommodates various optical systems for observing and photographing the cornea of the eye E to be examined. Reference symbol OA in the drawing denotes the optical axis of the objective lens 58 (see FIG. 4) provided in the lens barrel section 30, and corresponds to the optical axis of the imaging apparatus of the present invention.

Although not shown, the upper surface of the lens barrel 30 is provided with an inverter unit for converting the observed image of the cornea of the subject's eye E into an erected image when the observed image is obtained as an inverted image. The inverter section is provided with left and right eyepiece sections 32 . The operator (observer) views the subject's eye E binocularly by looking into the left and right eyepieces 32 .

A photographing unit 34 is detachably attached to the side surface of the lens barrel unit 30 . By attaching the photographing section 34 to the lens barrel section 30 in this way, the microscope main body 26 functions as the photographing device of the present invention. Note that the lens barrel section 30 and the photographing section 34 may be integrated.

A keratling light source support portion 38 that supports a keratling light source 36 and a button type detection sensor 39 (see FIG. 7) are provided on the lower surface of the lens barrel portion 30 .

The photographing unit 34 is, for example, a digital camera capable of photographing moving images. The photographing unit 34 photographs the cornea of the subject's eye E and outputs a photographed image 40 (image data) of the cornea. A photographed image 40 of the cornea photographed by the photographing unit 34 is output from the photographing unit 34 to a control device 42 which will be described later, and further displayed on a monitor 44 by the control device 42 . Thereby, the operator can observe the subject's eye E through the monitor 44 in addition to observing the subject's eye E through the left and right eyepieces 32 .

The keratizing light source 36 is a so-called ring illumination light source corresponding to the projection light source of the present invention. The keratling light source 36 is supported at a position between the microscope main body 26 and the subject's eye E by a keratling light source support 38 . The keratling light source 36 also has a projection axis PA collinear with the optical axis OA. Hereinafter, the optical axis OA and the projection axis PA are simply abbreviated as "optical axis OA".

FIG. 3 is a bottom view of the keratling light source 36 as viewed from below (the side of the subject's eye E). As shown in FIG. 3, the keratizing light source 36 is formed in a ring shape (including a substantially ring shape, the same shall apply hereinafter), and an opening hole 46 through which the optical axis OA passes is formed in the central portion thereof. Thereby, the microscope main body 26 observes and photographs the cornea of the subject's eye E through the aperture 46 of the keratling light source 36 .

A plurality of LEDs 48, which are a plurality of light emitting diodes, are arranged at equal intervals (including substantially equal intervals) on the lower surface of the keratling light source 36 along the same circumference around the optical axis OA. ing. Although the number of LEDs 48 arranged is not particularly limited, it is, for example, a multiple of 9, more specifically 36 in this embodiment. It should be noted that, instead of the LED 48, other semiconductor light sources or known various light sources such as halogen lamps may be used. Also, all or part of the LEDs 48 may be arranged at uneven intervals.

A supported portion 36a that is supported by a keratizing light source supporting portion 38, which will be described later, is provided on the outer peripheral portion of the keratizing light source 36. As shown in FIG. The supported portion 36a is provided with a pair of guide insertion holes 50 passing through the supported portion 36a in the vertical direction parallel to the optical axis OA, and one of the pair of guide insertion holes 50 extending from the side surface of the supported portion 36a. A bolt insertion hole 52 is formed.

A pair of guides 90, which are part of the keratling light source support portion 38, are respectively inserted through the pair of guide insertion holes 50, although the details will be described later. A bolt 92, which is a part of the keratling light source support portion 38, is inserted through the bolt insertion hole 52, although the details will be described later.

Returning to FIG. 2, when each LED 48 of the keratizing light source 36 is turned on (turned on), the keratizing light source 36 emits intermittent ring-shaped (dot-shaped) pattern light to the cornea of the eye E to be examined. A pattern 54 is projected. This ring pattern 54 corresponds to the measurement pattern of the present invention. Thereby, the photographing unit 34 photographs the cornea of the subject's eye E on which the ring pattern 54 is projected through the aperture 46 and outputs the photographed image 40 of the cornea to the control device 42 .

Although the details will be described later, the keratling light source support portion 38 selectively supports the keratling light source 36 at a plurality of positions along the vertical direction parallel to the optical axis OA.

The button type detection sensor 39 (see FIG. 7) is a known push button type detection sensor and corresponds to the detection section of the present invention. The button-type detection sensor 39 detects whether or not the keratling light source 36 is supported by the keratling light source support portion 38 at a specific position (retracted position, see FIG. 10), which will be described later in detail.

<Optical system of microscope body>
FIG. 4 is a schematic diagram of the optical system inside the microscope main body 26 when the microscope main body 26 is viewed from the side. FIG. 5 is a schematic diagram of the optical system inside the microscope main body 26 when the microscope main body 26 is viewed from the operator's side.

As shown in FIGS. 4 and 5, the microscope body 26 includes an objective lens 58, an illumination optical system 60, an observation optical system 70, and a photographing optical system 80.

The objective lens 58 is arranged at a position facing the aperture hole 46 (see FIG. 3) of the keratling light source 36, and has an optical axis OA that coincides with the projection axis PA (see FIG. 3). Note that the objective lens 58 is shared by the illumination optical system 60 , the observation optical system 70 , and the photographing optical system 80 .

(illumination optical system)
The illumination optical system 60 has an illumination optical axis OB that is not parallel to the optical axis OA, and irradiates the eye E to be inspected with illumination light. This illumination optical system 60 includes an illumination light source 61 , an optical fiber cable 62 , an exit aperture 63 , a condenser lens 64 , an illumination field aperture 65 , a slit plate 66 , a collimator lens 67 , an illumination prism 68 and an objective lens 58 .

The illumination light source 61 is provided outside the lens barrel section 30 . Also, the illumination light source 61 is connected to an entrance on one end side of an optical fiber cable 62 . The illumination light source 61 emits illumination light to one end of the optical fiber cable 62 .

The exit port on the other end side of the optical fiber cable 62 is arranged at a position facing the condenser lens 64 inside the lens barrel portion 30 . Thereby, the illumination light incident on one end of the optical fiber cable 62 from the illumination light source 61 is guided by the optical fiber cable 62 and emitted from the other end toward the condenser lens 64 .

An exit aperture 63 is arranged between the exit of the optical fiber cable 62 and the condenser lens 64 . The output aperture diaphragm 63 adjusts the output area of the illumination light emitted from the output port of the optical fiber cable 62 .

The condenser lens 64 collects the illumination light emitted from the optical fiber cable 62 and emits the illumination light toward the slit plate 66 via the illumination field stop 65 . The illumination field stop 65 is provided at a position optically conjugate with the front focal position of the objective lens 58, and adjusts the illumination field.

The slit plate 66 is formed of a disc-shaped member having light shielding properties. The slit plate 66 is selectively moved between a set position located on the illumination optical axis OB and a retracted position retracted from the set position in a direction perpendicular to the illumination optical axis OB by a drive mechanism (not shown). be done.

Further, the slit plate 66 is provided with a translucent portion composed of a plurality of slit holes 66a. Each slit hole 66a is formed at a position optically conjugate with respect to the aforementioned front focal position. The illumination light that has passed through each slit hole 66 a enters a collimator lens 67 .

The collimator lens 67 converts the illumination light that has passed through each slit hole 66 a into a parallel light flux, and emits the parallel light flux toward the illumination prism 68 .

The illumination prism 68 has a reflecting surface 68a that reflects the illumination light incident from the collimator lens 67 toward the objective lens 58 and the eye E to be examined. As a result, the illumination light reflected by the reflecting surface 68 a irradiates the subject's eye E via the objective lens 58 . Part of the illumination light applied to the eye E to be examined is reflected by the cornea of the eye E to be examined. The reflected light of the illumination light reflected by the cornea (also referred to as observation light or return light) travels through the objective lens 58 together with the reflected light of the ring pattern 54 reflected by the cornea. Incident into the optical system 80 . Thereby, the cornea of the subject's eye E on which the ring pattern 54 is projected can be observed through the observation optical system 70 , and the cornea can be photographed by the photographing optical system 80 .

(Observation optical system)
The observation optical system 70 is used to observe the cornea of the subject's eye E through the left and right eyepieces 32 . The observation optical system 70 includes an objective lens 58 and a pair of left and right observation optical systems 70L and 70R.

The left observation optical system 70L and the right observation optical system 70R are provided so as to sandwich the optical axis OA of the objective lens 58 therebetween. The left observation optical system 70L is an optical system corresponding to the operator's left eye, and has an observation optical axis OAL. The right observation optical system 70R is an optical system corresponding to the operator's right eye, and has an observation optical axis OAR.

The left observation optical system 70L and the right observation optical system 70R each have a zoom lens system 71, an imaging lens 73, an image erecting prism 74, an interpupillary adjustment prism 75, a field stop 76, and an eyepiece lens 77. In this embodiment, only the right observation optical system 70R has the beam splitter 72 between the zoom lens system 71 and the imaging lens 73. FIG. Also, the zoom lens system 71, the imaging lens 73, the image erecting prism 74, the interpupillary distance adjusting prism 75, and the field stop 76 constitute the relay optical system of the present invention.

The zoom lens system 71 includes a plurality of zoom lenses 71a, 71b, 71c. Each of the zoom lenses 71a to 71c can be moved in directions along the observation optical axes OAL and OAR by a lens driving mechanism (not shown). As a result, the zoom magnification for observing or photographing the cornea of the subject's eye E can be changed.

The imaging lens 73 collects reflected light from the cornea of the subject's eye E that has entered through the objective lens 58 and the zoom lens system 71 . The beam splitter 72 reflects part of the reflected light incident along the observation optical axis OAR from the zoom lens system 71 toward the imaging optical system 80 , and emits the rest of the reflected light toward the imaging lens 73 .

The image erecting prism 74 converts an inverted image of the cornea of the subject's eye E based on reflected light incident from the imaging lens 73 (left observation optical system 70L) or the beam splitter 72 (right observation optical system 70R) into an erect image. , the converted reflected light is emitted to the interpupillary distance adjusting prism 75 .

The interpupillary distance adjustment prism 75 adjusts the distance between the optical paths of the left observation optical system 70L and the right observation optical system 70R according to the operator's interpupillary distance (distance between the left and right eyes). A field stop 76 limits the field of view of the operator by blocking peripheral areas in the cross section of the reflected light.

The eyepieces 77 are provided on the left and right eyepieces 32, respectively. Thereby, the operator can directly observe the cornea of the subject's eye E on which the ring pattern 54 is projected through the eyepieces 77 of the left and right eyepieces 32 .

(Photography optical system)
The imaging optical system 80 is used for imaging the cornea of the eye E to be examined. This photographing optical system 80 has an objective lens 58 and shares a zoom lens system 71 and a beam splitter 72 with the right observing optical system 70R. The imaging optical system 80 also has an imaging lens 81 , a reflecting mirror 82 , and an imaging device 83 along a branched optical axis OC (imaging optical axis) branched from the observation optical axis OAR by the beam splitter 72 .

The imaging lens 81 forms an image of the reflected light reflected by the beam splitter 72 on the reflecting mirror 82 . The reflecting mirror 82 reflects the reflected light imaged by the imaging lens 81 toward the light receiving surface of the imaging element 83 in the imaging unit 34 .

The imaging element 83 is a CCD (charged-coupled device) type or CMOS (complementary metal-oxide-semiconductor) type area image sensor, and is provided in the imaging unit 34 . The imaging device 83 captures an image of reflected light incident from the reflecting mirror 82 and outputs a captured image 40 of the cornea of the eye E to be examined to the control device 42 . As a result, a photographed image 40 of the cornea of the subject's eye E on which the ring pattern 54 is projected is obtained. The operator can observe the cornea of the subject's eye E on which the ring pattern 54 is projected through the monitor 44 by causing the control device 42 to display the captured image 40 on the monitor 44 . Further, astigmatism information of the subject's eye E can be obtained by analyzing the photographed image 40 by the control device 42 .

<Keratling light source support>
FIG. 6 is a perspective view of the keratling light source support 38. As shown in FIG. As shown in FIG. 6, the keratizing light source support 38 selectively supports the keratizing light source 36 at a plurality of support positions along the optical axis OA (vertical direction). These support positions include a reference position, a first modified position, a second modified position, and a retracted position (see FIGS. 7-10). Note that the first change position and the second change position correspond to the change position of the present invention. Also, the reference position, the first changed position, and the second changed position correspond to two or more positions in the present invention.

The keratling light source support portion 38 is composed of a pair of guides 90 and one bolt 92 (a screw is also acceptable).

The pair of guides 90 are provided on the lower surface of the lens barrel section 30 and have a linear shape (bar shape) extending downward in a direction parallel to the optical axis OA. Each guide 90 is inserted through a pair of guide insertion holes 50 respectively formed in the supported portion 36a as shown in FIG. Thereby, the keratling light source 36 is movably supported by each guide 90 along the optical axis OA.

Four bolt holes 90a (female threads) are formed in one outer peripheral surface of the pair of guides 90 (see FIGS. 7 to 10). Each bolt hole 90a is formed on the outer peripheral surface of the guide 90 at intervals along the optical axis OA. The tip of a bolt 92 inserted through the bolt insertion hole 52 (see FIG. 3) of the supported portion 36a is screwed into each bolt hole 90a.

The bolt 92 corresponds to the fixing member of the present invention, and is screwed into one of the bolt holes 90a after being inserted through the bolt insertion hole 52 of the supported portion 36a. Thus, the keratling light source 36 can be releasably fixed to the guide 90 at a position corresponding to one of the bolt holes 90a. Therefore, by adjusting the position of each bolt hole 90a formed on the outer peripheral surface of the bolt 92, the guide 90 can support the keratling light source 36 at a plurality of desired supporting positions along the optical axis OA. It can be selectively supported at a modified position, a second modified position, and a retracted position.

Instead of selectively releasably fixing the keratizing light source 36 to each support position with the bolts 92 with respect to the guide 90, for example, a locking mechanism (corresponding to the fixing member of the present invention) such as a click mechanism is used. can be selectively releasably secured (locked) to each support position.

FIG. 7 is an explanatory diagram for explaining the reference position of the keratling light source 36. As shown in FIG. The symbol WD in the drawing indicates the working distance, which is the distance between the subject's eye E and the objective lens 58 of the microscope main body 26 . Further, symbol d in the drawing indicates a light source distance (equivalent to the distance of the present invention), which is the distance between the subject's eye E and the keratling light source 36 .

As shown in FIG. 7, the tip of the bolt 92 inserted through the bolt insertion hole 52 of the supported portion 36a (hereinafter simply referred to as "the tip of the bolt 92") is positioned in the lowest direction in each bolt hole 90a. The keratling light source 36 is supported at the reference position by the guide 90 by screwing it into the bolt hole 90a located at . This reference position is a position where the light source distance d becomes a predetermined light source distance reference value (corresponding to the reference value of the present invention) when the working distance WD is set to a predetermined working distance reference value. Specifically, the light source distance reference value is the distance at which the diameter of the ring pattern 54 projected from the keratizing light source 36 onto the cornea of the subject's eye E is approximately 3φ (mm) on the cornea.

FIG. 8 is an explanatory diagram for explaining the first changed position of the keratling light source 36. As shown in FIG. By screwing the tip of the bolt 92 into the bolt hole 90a located second from the bottom among the bolt holes 90a, the working distance WD can be adjusted to the guide 90 while maintaining the working distance reference value. supports the keratling light source 36 in the first modified position. The first change position is a position shifted upward (retracted) from the reference position and is a position where the button-type detection sensor 39 is not pressed. When the keratling light source 36 is supported in the first modified position, the light source distance d is increased compared to when it is supported in the reference position.

FIG. 9 is an explanatory diagram for explaining the second changed position of the keratling light source 36. As shown in FIG. As shown in FIG. 9, by screwing the tip of the bolt 92 into the third bolt hole 90a from the bottom among the bolt holes 90a, the working distance WD can be adjusted to the working distance reference value. In this state, the guide 90 supports the keratling light source 36 in the second modified position. The second change position is a position shifted upward (retracted) from the first change position and is a position where the button-type detection sensor 39 is not pressed. When the keratling light source 36 is supported in the second modified position, the light source distance d increases more than when supported in the first modified position.

FIG. 10 is an explanatory diagram for explaining the retracted position of the keratling light source 36. As shown in FIG. As shown in FIG. 10, the keratling light source 36 is supported by the guide 90 at the retracted position by screwing the tip of the bolt 92 into the bolt hole 90a positioned most upward among the bolt holes 90a. be. The retracted position is a position for retracting the keratling light source 36 when not using the keratizing light source 36 in cataract surgery. Specifically, the retracted position is a position shifted upward (retracted) from the second change position and at which the button-type detection sensor 39 is pressed.

When the keratling light source 36 moves to the retracted position, the button type detection sensor 39 is pressed by the keratling light source 36 . Thus, based on the detection result of the button type detection sensor 39, it is possible to detect whether the keratling light source 36 is supported by the guide 90 at the retracted position. Incidentally, instead of the button-type detection sensor 39, various known sensors such as an optical sensor (ranging sensor) and a contact detection sensor are used to detect whether or not the keratling light source 36 is supported at the retracted position. good too.

By supporting the keratling light source 36 movably along the optical axis OA by the keratling light source supporting portion 38 in this manner, the keratling light source 36 can be moved to a first changed position, a second changed position, and a position different from the reference position. Each can be supported in a retracted position. As a result, only the light source distance d can be changed while the working distance WD is maintained at the working distance reference value.

FIG. 11 is an explanatory diagram for explaining the relationship between the support position of the keratizing light source 36 by the guide 90 and the ring pattern 54 projected from the keratizing light source 36 onto the cornea of the eye E to be examined.

When the position at which the keratling light source 36 is supported by the guide 90 is changed from the reference position to the first changed position, the light source distance d of the keratling light source 36 increases. Therefore, the diameter of the ring pattern 54 projected onto the cornea of the eye to be examined E from the keratling light source 36 at the reference position is larger than the diameter of the ring pattern 54 (see symbol XIA in the drawing). The diameter of the ring pattern 54 projected onto the cornea (see symbol XIB in the figure) is reduced.

When the position at which the keratling light source 36 is supported by the guide 90 is changed from the first change position to the second change position, the light source distance d of the keratling light source 36 further increases. For this reason, the diameter of the ring pattern 54 projected onto the cornea of the eye to be examined E from the kerating light source 36 at the first changed position (see symbol XIB in the figure) is larger than the diameter of the ring pattern 54 projected from the kerating light source 36 at the second changed position to the eye to be examined. The diameter of the ring pattern 54 projected onto the cornea of E (see symbol XIC in the figure) becomes smaller.

By providing the reference position, the first change position, and the second change position as the support positions of the keratling light source 36 by the keratling light source support section 38 in this way, the ring pattern 54 projected onto the cornea of the eye E to be examined can be changed. You can change the size in 3 stages. Reflected light from the cornea of the subject's eye E onto which the ring pattern 54 is projected enters the objective lens 58 through the aperture 46 of the keratling light source 36 at each supporting position of the keratizing light source 36, and the objective lens 58 and The light is guided to the eyepiece lens 77 and the imaging device 83 through each optical system.

<Control device>
FIG. 12 is a functional block diagram of the control device 42 of the first embodiment. As shown in FIG. 12, the control device 42 is provided inside the microscope main body 26 or the first arm 16, for example. Also, the control device 42 may be a computer externally connected to the surgical microscope 10 .

The control device 42 includes an arithmetic circuit composed of various processors, memories, and the like. Various processors include CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), and programmable logic devices [for example, SPLD (Simple Programmable Logic Devices), CPLD (Complex Programmable Logic Device), and FPGAs (Field Programmable Gate Arrays)]. Various functions of the control device 42 may be realized by one processor, or may be realized by a plurality of processors of the same type or different types.

In addition to the driving device 24, the keratling light source 36, the button-type detection sensor 39, the illumination optical system 60, the observation optical system 70, and the photographing optical system 80 (the photographing section 34), the control device 42 includes: An operation unit 96 and a storage unit 98 are connected.

The operation unit 96 performs a position and orientation adjustment operation (manual alignment operation) of the microscope main body 26, a lighting operation of the illumination light source 61, a measurement start operation of the astigmatism information of the subject's eye E, and a zoom magnification of the imaging optical system 80. It accepts input of various operations of the surgical microscope 10 including changing operations. The operation unit 96 includes hardware keys (buttons, switches, etc.) provided on the microscope main body 26 or an operation panel in addition to the foot switch 22 described above.

Although not shown, the storage unit 98 stores a control program for the surgical microscope 10, measurement results of astigmatism information of the eye E to be examined, and the like.

By reading and executing the control program in the storage unit 98, the control device 42 controls the drive control unit 100, the ring control unit 102, the optical system control unit 104, the image acquisition unit 106, the astigmatism information calculation unit 108, the display control unit. 110 and a notification control unit 112 . In what follows, what is described as ``section'' of the control device 42 may be ``circuit'', ``equipment'', or ``equipment''. That is, what is described as "--unit" may consist of firmware, software, hardware, or a combination thereof.

The drive control unit 100 controls driving of the drive device 24 . The drive control unit 100 drives the drive device 24 to adjust the position and orientation of the microscope main body 26 according to the operator's operation input to the operation unit 96 (foot switch 22). Thereby, the microscope body 26 is manually aligned with the eye E to be examined.

The ring control section 102 corresponds to the light source control section of the present invention, and controls lighting and extinguishing of each LED 48 of the keratizing light source 36 . Based on the detection result of the button-type detection sensor 39, the ring control unit 102 turns off each LED 48 of the keratling light source 36 when the keratling light source 36 is supported at the retracted position. As a result, the keratling light source 36 can be automatically extinguished simply by moving the keratling light source 36 to the retracted position.

In addition, based on the detection result of the button-type detection sensor 39, the ring control unit 102 causes the keratling light source support unit 38 to move the keratling light source 36 to a support position (reference position, first change position, second change position) different from the retracted position. position), each LED 48 of the keratling light source 36 is automatically turned on. Instead of automatically lighting each LED 48 , the ring control unit 102 may light each LED 48 according to an input of an astigmatism information measurement start operation to the operation unit 96 .

Further, the ring control unit 102 changes the lighting mode (light emission mode) of one or more LEDs 48 selected from among the LEDs 48 of the keratizing light source 36 under the control of the notification control unit 112, which will be described later.

The optical system control unit 104 controls the illumination optical system 60 , observation optical system 70 , and imaging optical system 80 . The optical system control unit 104 turns on the illumination light source 61 of the illumination optical system 60 when an operation to turn on the illumination light source 61 is input to the operation unit 96 . Further, when an astigmatism information measurement start operation is input to the operation unit 96 , the optical system control unit 104 causes the imaging device 83 of the imaging optical system 80 to capture reflected light from the eye E to be examined. As a result, the cornea of the subject's eye E on which the ring pattern 54 is projected is photographed by the photographing optical system 80 (the photographing unit 34), and the photographed image 40 thereof is output.

In addition, the optical system control unit 104 drives the zoom lens systems 71 of the left observation optical system 70L and the right observation optical system 70R in response to an input of a zoom magnification change operation to the operation unit 96 to observe the eye E to be examined. Change the zoom magnification when shooting or when shooting.

The image acquisition unit 106 acquires the photographed image 40 of the cornea of the subject eye E and the ring pattern 54 from the imaging device 83 of the photographing optical system 80 via an interface (not shown), and uses the photographed image 40 as an astigmatism information calculation unit 108. and the display control unit 110, respectively.

The astigmatism information calculation unit 108 calculates astigmatism information such as the astigmatism power and astigmatism axis direction of the subject eye E based on the photographed image 40 of the cornea and ring pattern 54 of the subject eye E input from the image acquisition unit 106 . Specifically, the astigmatism information calculation unit 108 detects the ring pattern 54 from the captured image 40, and calculates the astigmatism power of the subject's eye E from the ellipticity (ratio of minor axis to major axis) of the ring pattern 54. , the astigmatism axis direction of the subject's eye E is calculated from the elliptical principal axis direction of the ring pattern 54 . A specific method for calculating the degree of astigmatism and the direction of the axis of astigmatism is known technology (see Patent Literatures 1 and 2 above), so a detailed description thereof will be omitted here.

Further, the astigmatism information calculation unit 108 outputs the calculation result of the astigmatism information of the subject's eye E to the notification control unit 112 described later and stores it in the storage unit 98 .

The display control unit 110 causes the monitor 44 to display the captured image 40 input from the image acquisition unit 106 . Thereby, the operator can observe the cornea of the subject's eye E and the ring pattern 54 projected on the cornea through the monitor 44 . Under the control of the notification control unit 112, which will be described later, the display control unit 110 superimposes an index 113 (see FIG. 12) indicating the astigmatism axis direction of the subject's eye E on the captured image 40 displayed on the monitor 44. Let

FIG. 13 is an explanatory diagram for explaining the notification control of the astigmatism axis direction of the subject's eye E by the notification control unit 112 . As shown in FIG. 13 and FIG. 12 already described, the notification control unit 112 controls the keratling light source 36 ( At least one of the LEDs 48) and the monitor 44 is controlled to notify the operator of the astigmatism axis direction of the eye E to be examined.

As indicated by symbol XIIIA in FIG. 13, the notification control unit 112, when performing notification of the astigmatism axis direction of the subject's eye E using the LEDs 48 of the keratling light source 36, based on the calculation result of the astigmatism axis direction. , the LED 48 corresponding to the astigmatism axis direction of the eye E to be inspected is selected. Next, based on this selection result, the notification control unit 112 controls the ring control unit 102 to change the lighting mode of the LED 48 corresponding to the astigmatism axis direction of the eye E to be examined, for example, to blink it. As a result, among the 36 luminescent spot images forming the ring pattern 54 projected onto the cornea of the subject's eye E, the luminescent spot image corresponding to the blinking LED 48 starts blinking. As a result, the astigmatic axis direction of the subject's eye E can be notified to the operator observing the subject's eye E through the left and right eyepieces 32 .

In addition to blinking of the LED 48, the change of the lighting mode of the LED 48 includes, for example, turning off the LED 48 and changing the luminance. Moreover, when each of the 36 LEDs 48 is composed of LEDs of a plurality of colors, the emission colors of the LEDs 48 may be changed.

As indicated by symbol XIIIB in FIG. 13 , the notification control unit 112 analyzes the captured image 40 displayed on the monitor 44 when performing notification of the astigmatism axis direction of the eye E using the monitor 44. , 36 luminescent spot images forming the ring pattern 54 are detected from the photographed image 40 . Next, based on the calculation result of the astigmatism axis direction of the subject's eye E by the astigmatism information calculation unit 108, the notification control unit 112 selects the 36 bright spot images in the photographed image 40 corresponding to the astigmatism axis direction of the subject's eye E. Select the luminescent spot image to be displayed. Then, based on this selection result, the notification control unit 112 controls the display control unit 110 to display the index 113 indicating the bright spot image corresponding to the astigmatism axis direction of the eye E to be inspected. It is displayed superimposed on the image 40 .

The shape (pattern), color, and display mode of the index 113 are not particularly limited as long as the bright spot image corresponding to the astigmatic axis direction of the eye to be examined E can be identified in the photographed image 40. For example, a reticle (crosshairs) and the like are used.

In this embodiment, since the keratizing light source 36 is provided with 36 LEDs 48, the operator can be notified of the astigmatism axis direction of the subject's eye E with a sensitivity of "360°/36=10°". Also, considering the spaces between the 36 LEDs 48, for example, by blinking two adjacent LEDs 48 or displaying the index 113 between two adjacent bright spot images on the monitor 44, , 5 degrees, the operator can be notified of the astigmatism axis direction of the eye E to be examined.

<Action of First Embodiment>
FIG. 14 is a flow chart showing the flow of measurement of astigmatism information of the subject's eye E and notification of the astigmatism axis direction by the surgical microscope 10 of the first embodiment having the above configuration. It is assumed that the keratling light source 36 is supported at the retracted position by the keratling light source support portion 38 in the initial state.

As shown in FIG. 14, first, the operator performs operation input for adjusting the position and attitude of the microscope main body 26 to the foot switch 22 of the operation section 96 . Accordingly, the drive control unit 100 drives the drive device 24 to perform manual alignment for adjusting the position and orientation of the microscope main body 26 with respect to the eye E (step S1).

Next, the operator inputs a turn-on operation of the illumination light source 61 to the operation unit 96 . Also, the operator operates the keratling light source support section 38 to change the support position of the keratling light source 36 from the retracted position to the reference position. Thereby, the optical system control unit 104 turns on the illumination light source 61 and the ring control unit 102 turns on each LED 48 of the keratizing light source 36 . When the illumination light source 61 and the LEDs 48 are turned on, the illumination optical system 60 irradiates the cornea of the subject's eye E with illumination light, and the LEDs 48 project the ring pattern 54 onto the cornea (step S2). As a result, the operator can observe the cornea of the subject's eye E on which the ring pattern 54 is projected through the left and right eyepieces 32 . Note that the order of steps S1 and S2 may be reversed.

Then, the operator inputs an operation to start measuring the astigmatism information of the subject's eye E to the operation unit 96 . As a result, the optical system control unit 104 causes the imaging element 83 of the imaging optical system 80 to start imaging the reflected light from the eye E to be examined. As a result, the photographing of the cornea of the subject's eye E on which the ring pattern 54 is projected and the output of the photographed image 40 are executed by the photographing optical system 80, and the image acquisition unit 106 obtains the photographed image 40 and the display control unit 110 and output of the captured image 40 to the astigmatism information calculation unit 108 (step S3).

The display control unit 110 that has acquired the captured image 40 from the image acquisition unit 106 displays this captured image 40 on the monitor 44 (step S4). Thereby, the operator can observe the cornea of the subject's eye E on which the ring pattern 54 is projected through the monitor 44 .

Further, the astigmatism information calculation unit 108 that has acquired the captured image 40 from the image acquisition unit 106 calculates astigmatism information including the astigmatism power and astigmatism axis direction of the subject eye E by a known method based on the captured image 40, and this calculation The result is stored in the storage unit 98 and output to the notification control unit 112 (step S5).

The notification control unit 112 that has received the astigmatism information (astigmatism axis direction) input from the astigmatism information calculation unit 108 controls the ring control unit 102 based on this astigmatism information to turn on the LED 48 corresponding to the astigmatism axis direction of the eye E to be examined. Blink (see symbol XIIIA in FIG. 13). Alternatively, the notification control unit 112 controls the display control unit 110 based on this astigmatism information to display the index 113 indicating the bright spot image corresponding to the astigmatism axis direction of the eye E to be inspected on the captured image 40 within the display screen of the monitor 44. It is superimposed and displayed (see symbol XIIIB in FIG. 13). As a result, the operator can be notified of the astigmatism axis direction of the subject's eye E (step S6).

When the measurement of the astigmatism information of the subject's eye E corresponding to the reference position is completed, the operator operates the keratling light source supporter 38 to change the position of the keratling light source 36 from the reference position to the first change position (step YES in S7, S8). As a result, the light source distance d of the keratizing light source 36 increases, so that the diameter of the ring pattern 54 projected from the keratizing light source 36 onto the cornea of the subject's eye E is 1, as indicated by XIB in FIG. gradually smaller.

Next, when the operator inputs an operation to start measuring the astigmatism information of the subject's eye E to the operation unit 96, the processes from step S3 to step S6 are repeatedly executed, and the subject's eye corresponding to the first changed position is Measurement and storage of E astigmatism information, and notification of the astigmatism axis direction are performed.

When the measurement of the astigmatism information of the subject's eye E corresponding to the first changed position is completed, the operator operates the keratling light source support section 38 to change the position of the keratling light source 36 from the first changed position to the second changed position. (YES in step S7, step S8). 11, the light source distance d of the keratizing light source 36 further increases, so that the diameter of the ring pattern 54 projected from the keratizing light source 36 onto the cornea of the eye to be examined E is is one step smaller.

Then, when the operator inputs an operation to start measuring the astigmatism information of the subject's eye E to the operation unit 96, the processes from step S3 to step S6 are repeatedly executed, and the subject's eye corresponding to the second change position is Measurement and storage of E astigmatism information, and notification of the astigmatism axis direction are performed. As a result, the astigmatism information of the subject's eye E can be measured at each of the reference position, the first changed position, and the second changed position. As a result, even if the pupil diameter of the eye to be examined E is smaller than a general pupil diameter, astigmatism information of the eye to be examined E that matches the pupil diameter of the eye to be examined E can be obtained.

When the measurement of the astigmatism information of the subject's eye E is completed, the operator operates the keratling light source supporter 38 to change the position of the keratling light source 36 from the second change position to the retracted position (NO in step S7). . As a result, the button-type detection sensor 39 is pressed by the keratling light source 36 as shown in FIG. As a result, the ring control unit 102 turns off each LED 48 of the keratizing light source 36 based on the detection result of the button type detection sensor 39 .

In FIG. 14, the astigmatism information of the eye to be examined E is measured at each position of the reference position, the first changed position, and the second changed position. Astigmatism information may be measured only by position. In this case, after step S2 (when the subject's eye E is observed through the left and right eyepieces 32) or step S4 (when the subject's eye E is observed through the monitor 44), the position of the keratling light source 36 is is changed to a position (first change position or second change position) where the ring pattern 54 matching the pupil diameter of the eye E can be projected (step S8). Then, the processes from step S3 to step S6 described above are executed.

<Effects of the first embodiment>
As described above, in the first embodiment, the ring pattern 54 is projected onto the cornea of the subject's eye E from the keratizing light source 36 supported at positions (the first changed position and the second changed position) different from the reference position, and Since the cornea of the subject's eye E onto which the ring pattern 54 is projected can be imaged, astigmatism information that matches the pupil diameter of the subject's eye E can be obtained.

In addition, in the first embodiment, the keratling light source 36 can be selectively supported at three different positions: the reference position, the first change position, and the second change position. Three types of ring patterns 54 having different sizes (diameters) can be projected onto the cornea of the eye E to be examined. As a result, the same effect as having a plurality of keratling light sources 36 of different sizes can be obtained.

[Second embodiment]
<Configuration of Second Embodiment>
FIG. 15 is a functional block diagram of the control device 42A of the surgical microscope 10 of the second embodiment. In the first embodiment, the astigmatism information of the eye to be examined E is measured at each position of the reference position, the first changed position, and the second changed position, but in the second embodiment, the corneal curvature ( corneal shape) is measured.

As shown in FIG. 15, the surgical microscope 10 of the second embodiment has a control device 42A different from that of the first embodiment, except that the positional relationship information 116 is stored in the storage unit 98. The configuration is basically the same as that of the first embodiment. For this reason, the same reference numerals are given to the same functions or configurations as those of the first embodiment, and the description thereof will be omitted.

The control device 42A functions as a corneal curvature calculation section 114 in addition to each section of the control device 42 of the first embodiment.

Every time the image acquisition unit 106 of the second embodiment acquires the captured image 40 of the cornea and the ring pattern 54 of the eye to be examined E from the imaging optical system 80, the captured image 40 is captured by the display control unit 110 and the astigmatism. The information is output to the corneal curvature calculation unit 114 in addition to the information calculation unit 108 . Accordingly, the corneal curvature calculation unit 114 obtains three types of captured images 40 captured by the imaging optical system 80 at three types of positions (reference position, first changed position, and second changed position) of the keratling light source 36 . to get Hereinafter, among the three types of captured images 40, the captured image 40 corresponding to the reference position is referred to as a reference position image 40A, the captured image 40 corresponding to the first changed position is referred to as a first changed position image 40B, and the second changed position. Let the corresponding captured image 40 be a second changed position image 40C.

The positional relationship information 116 indicates respective relative positions of the first changed position and the second changed position with respect to the reference position. For example, the positional relationship information 116 is the height position (mm) in the vertical direction (direction of the optical axis OA) of each of the first change position and the second change position when the reference position is 0 (mm). This positional relationship information 116 is used for calculation of the corneal curvature of the subject's eye E by the corneal curvature calculation unit 114, which will be described later, and is stored in advance in the storage unit 98 by the manufacturer.

The corneal curvature calculation unit 114 calculates the corneal curvature of the subject's eye E based on two or more of the three types of captured images 40 acquired from the image acquisition unit 106 and the positional relationship information 116 acquired from the storage unit 98. perform the calculation of In this case, the corneal curvature calculation unit 114 functions as the relative position acquisition unit of the present invention together with the storage unit 98 described above.

FIG. 16 is an explanatory diagram for explaining a first example of calculation of the corneal curvature of the subject's eye E by the corneal curvature calculator 114 . FIG. 17 is an explanatory diagram for explaining a second example of calculation of the corneal curvature of the subject's eye E by the corneal curvature calculator 114 .

As shown in FIG. 16 and FIG. 15 already described, in the first example, the corneal curvature calculation unit 114 calculates the reference position image 40A (see symbol XVIA) among the three types of captured images 40 acquired from the image acquisition unit 106. and the second changed position image 40C (see symbol XVIB), the corneal curvature of the subject's eye E is calculated. In this case, the corneal curvature calculator 114 divides and detects two types of ring patterns 54 from the reference position image 40A and the second change position image 40C. Thus, a process substantially equivalent to detecting the double ring pattern 54 from the photographed image 40D (see symbol XVIC) of the cornea of the subject's eye E on which the double ring pattern 54 is projected by a keratometer or the like. It can be performed.

At this time, the light source distance d differs between when the reference position image 40A is captured and when the second changed position image 40C is captured. Therefore, the corneal curvature calculator 114 calculates the difference between the light source distance d corresponding to the reference position and the light source distance d corresponding to the second change position based on the positional relationship information 116 . Then, the corneal curvature calculator 114 calculates the corneal curvature of the subject's eye E based on the two types of ring patterns 54 and the calculation result of the difference in the light source distance d. Since a specific method for calculating the corneal curvature is a known technique, a specific description is omitted here.

As shown in FIG. 17 and FIG. 15 already described, in the second example, the corneal curvature calculation unit 114 acquires the reference position image 40A (see symbol XVIIA) and the first change position image 40B (see symbol XVIIA) acquired from the image acquisition unit 106. XVIIB) and the second changed position image 40C (see symbol XVIIC), the corneal curvature of the subject's eye E is calculated. In this case, the corneal curvature calculator 114 divides and detects three types of ring patterns 54 from the reference position image 40A, the first changed position image 40B, and the second changed position image 40C. Thereby, a process substantially equivalent to detecting the triple ring pattern 54 from the photographed image 40E (see symbol XVIID) of the cornea of the eye to be examined E on which the triple ring pattern 54 is projected by a keratometer or the like. It can be performed.

Further, the corneal curvature calculator 114 calculates a first difference between the light source distance d corresponding to the reference position and the light source distance d corresponding to the first changed position based on the positional relationship information 116 as in the first example. Also, a second difference between the light source distance d corresponding to the reference position and the light source distance d corresponding to the second changed position is calculated. Then, the corneal curvature calculator 114 calculates the corneal curvature of the subject's eye E based on the three types of ring patterns 54 and the calculation results of the first difference and the second difference of the light source distance d.

Further, although illustration is omitted, the corneal curvature calculation unit 114 calculates the corneal curvature of the subject's eye E based on the reference position image 40A and the first changed position image 40B, The corneal curvature of the subject's eye E can be calculated based on 40C. The corneal curvature of the subject eye E is calculated by the corneal curvature calculator 114 from among the three types of captured images 40 (the reference position image 40A, the first changed position image 40B, and the second changed position image 40C). A selection operation for selecting two or more captured images 40 is performed by the operation unit 96 .

The corneal curvature calculation unit 114 outputs the calculation result of the corneal curvature of the eye E to be examined to the display control unit 110 and the storage unit 98, respectively. As a result, the calculation result of the corneal curvature is displayed on the monitor 44 and stored in the storage unit 98 by the display control unit 110 .

<Action of Second Embodiment>
FIG. 18 is a flow chart showing the flow of calculation processing of the corneal curvature of the subject's eye E by the surgical microscope 10 of the second embodiment configured as described above. Here, as indicated by symbol XVIIB in FIG. 17, the corneal curvature calculator 114 calculates the corneal curvature of the subject's eye E based on all of the reference position image 40A, the first changed position image 40B, and the second changed position image 40C. A case of calculating is described as an example.

Since the processing from step S1 to step S2 is basically the same as that of the first embodiment shown in FIG. 14, detailed description thereof will be omitted here. The measurement of astigmatism information of the subject's eye E and the notification of the astigmatism axis direction are also the same as those in the first embodiment, so a detailed description thereof will be omitted here.

After step S2 is completed, when the operator inputs an imaging start operation to the operation unit 96, imaging of the reference position image 40A by the imaging optical system 80, acquisition of the reference position image 40A by the image acquisition unit 106, and image acquisition are performed. and outputting the reference position image 40A from the unit 106 to the corneal curvature calculation unit 114 and the like (step S3).

When the imaging of the reference position image 40A and the like are completed, the operator operates the keratling light source support section 38 to change the position of the keratling light source 36 from the reference position to the first changed position (step S4A).

After changing the position of the keratling light source 36, when the operator inputs a photographing start operation to the operation unit 96, the first changed position image 40B is photographed by the photographing optical system 80, and the first changed position image 40B is photographed by the image acquisition unit 106. Acquisition of the image 40B and output of the first change position image 40B from the image acquisition unit 106 to the corneal curvature calculation unit 114 and the like are executed (step S5A).

When the imaging of the first change position image 40B is completed, the operator operates the keratling light source support section 38 to change the position of the keratling light source 36 from the first change position to the second change position (step S6A). YES, step S4A).

After changing the position of the keratling light source 36, when the operator inputs an imaging start operation to the operation unit 96, the imaging optical system 80 captures the second changed position image 40C and the image acquisition unit 106 captures the second changed position image 40C. Acquisition of the image 40C and output of the second changed position image 40C from the image acquisition unit 106 to the corneal curvature calculation unit 114 and the like are executed (step S5A).

Next, when the operator inputs an operation to start the calculation of the corneal curvature of the subject's eye E to the operation unit 96, the corneal curvature calculation unit 114 acquires the positional relationship information 116 from the storage unit 98 (NO in step S6A, step S7A). ). Then, the corneal curvature calculation unit 114 calculates the three types of ring patterns 54 detected from the reference position image 40A, the first changed position image 40B, and the second changed position image 40C, and the positional relationship information 116 acquired from the storage unit 98. , and the corneal curvature of the subject's eye E is calculated (step S8A).

The result of calculation of the corneal curvature of the subject's eye E by the corneal curvature calculation unit 114 is displayed on the monitor 44 by the display control unit 110 and stored in the storage unit 98 (step S9A).

In FIG. 18, the cornea is photographed by the photographing optical system 80 at each of three positions (reference position, first changed position, second changed position) of the keratling light source 36. It is not necessary to shoot at all. For example, when the corneal curvature calculation unit 114 calculates the corneal curvature based on any two of the reference position image 40A, the first changed position image 40B, and the second changed position image 40C, three types of The imaging unit 34 performs imaging only at two types of positions selected from the positions.

<Effects of Second Embodiment>
As described above, in the second embodiment, the position of the kerating light source 36 is sequentially changed to two or more positions along the direction of the optical axis OA, and the cornea is photographed by the photographing optical system 80 for each of the two or more positions. By doing so, it is possible to divide each photographed image 40 and detect the multiple ring patterns 54 that are two or more. As a result, even if the keratizing light source 36 is of a type that projects a single ring pattern 54 onto the cornea of the eye E to be examined, the corneal curvature of the eye E to be examined can be calculated. Further, as described in the first embodiment, the corneal curvature and astigmatism information of the eye to be examined E can be measured simultaneously by simultaneously calculating the astigmatism information of the eye to be examined E for each captured image 40 .

[Modified example of configuration of each embodiment]
Next, a modified example of a partial configuration of the surgical microscope 10 of each of the above-described embodiments will be described. It should be noted that the same reference numerals are given to the same functions or configurations as those of the above-described embodiments, and the description thereof will be omitted. Moreover, you may combine several modifications suitably.

<Modified example of keratling light source>
FIG. 19 is a bottom view of keratling light sources 36A and 36B, which are modifications of the keratling light source 36 of each of the above embodiments. The keratling light source 36 of each of the above embodiments projects a single ring pattern 54 onto the cornea of the eye E to be examined. As shown in FIG. A ring pattern 54 (see FIGS. 16 and 17) is projected.

As indicated by symbol XIXA in FIG. 19, a plurality of LEDs 48 are arranged at equal intervals along double concentric circles centered on the optical axis OA on the lower surface of the keratling light source 36A. Further, as indicated by XIXB in FIG. 19, a plurality of LEDs 48 are arranged at regular intervals along triple concentric circles centered on the optical axis OA on the lower surface of the keratling light source 36B. This allows the keratizing light sources 36A and 36B to project a concentric ring pattern 54 onto the cornea. Instead of the keratling light sources 36A and 36B, a keratling light source (not shown) capable of projecting four or more concentric ring patterns 54 onto the cornea may be used.

By applying the keratizing light sources 36A and 36B to the first embodiment, a plurality of positions of the subject's eye E can be detected for each position (reference position, first change position, second change position) of the keratling light sources 36A and 36B. Astigmatism information (for each ring pattern 54) is obtained.

By applying the keratizing light sources 36A and 36B to the second embodiment, multiple ring patterns 54 can be divided and projected onto the cornea of the eye E to be examined. For example, when the number of types of positions of the keratling light sources 36A and 36B is N (here, N is 2 or 3), when the keratling light source 36A is applied to the second embodiment, "2N , the multiple ring pattern 54 can be divided and projected. Further, when the keratizing light source 36B is applied to the second embodiment, the ring pattern 54 of "3N" folds can be divided and projected onto the cornea. Thereby, the corneal curvature of the subject's eye E can be measured with high accuracy.

When the keratizing light sources 36A and 36B are applied to the above-described second embodiment, the corneal curvature is calculated based on the photographed image 40 obtained by one photographing by the photographing optical system 80, similarly to the conventional keratometer or the like. The calculator 114 can calculate the corneal curvature of the eye E to be examined.

<Modified example of ring pattern>
FIG. 20 is an explanatory diagram of a ring pattern 54A, which is a modification of the ring pattern 54 projected onto the cornea of the subject's eye E from the keratizing light source 36 of each of the above embodiments. Here, XXA in FIG. 20 indicates the ring pattern 54A corresponding to the reference position. XXB in FIG. 20 indicates the ring pattern 54A corresponding to the first change position, and XXC indicates the ring pattern 54A corresponding to the second change position.

In each of the above-described embodiments, by providing a plurality of LEDs 48 on the lower surface of the keratling light source 36, the intermittent ring-shaped ring pattern 54 is projected from the keratling light source 36 onto the cornea of the subject's eye E. Instead of each LED 48, a known ring light (not shown) may be provided on the lower surface of the kerato-ring light source 36. FIG. As a result, a continuous ring pattern 54A can be projected onto the cornea of the subject's eye E from the keratling light source 36, as indicated by XXA, XXB, and XXC in FIG.

Instead of projecting the single ring pattern 54A from the keratizing light source 36 onto the cornea of the eye E to be examined, multiple concentric ring patterns 54A may be projected onto the cornea.

<Modified Example of Keratling Light Source Supporting Part>
FIG. 21 is an explanatory diagram for explaining a keratling light source support portion 38A that is a modification of the keratling light source support portion 38 of each of the above-described embodiments. FIG. 22 is a functional block diagram of the control device 42B of the surgical microscope 10 including the keratling light source support 38A shown in FIG.

In the keratling light source support 38 of each embodiment described above, the position of the keratling light source 36 needs to be manually changed by the operator. However, as shown in FIG. A change in the position of the light source 36 is performed by an actuator 150 .

The keratling light source support 38A includes an actuator 150, a linear position detection sensor 152, and a scale 154. As shown in FIG.

The actuator 150 is fixed (or integrally formed) to the supported portion 36a, and moves integrally with the keratling light source 36 along the pair of guides 90 under the control of the control device 42B. As the actuator 150, various known linear actuators such as a linear motor, a motor drive mechanism, and a lead screw mechanism are used. This allows the actuator 150 to selectively support the keratling light source 36 at a number of modified positions along the optical axis OA other than the reference position. That is, the actuator 150 can continuously change the supporting position of the keratling light source 36 .

The linear position detection sensor 152 is provided, for example, on the actuator 150 and reads scales 154 (also referred to as graduations) provided on the pair of guides 90 . This makes it possible to detect the position of the keratling light source 36 in the direction (vertical direction) along the optical axis OA.

At this time, by setting the graduation of the scale 154 corresponding to the reference position to "0 (mm)", the relative position of the keratling light source 36 with respect to the reference position can be determined based on the reading result of the scale 154 by the linear position detection sensor 152. can be detected. Therefore, the linear position detection sensor 152 and the scale 154 constitute the relative position acquisition section of the present invention. Then, the linear position detection sensor 152 outputs the reading result of the scale 154, that is, the position detection result of the keratling light source 36 to the control device 42B.

As shown in FIG. 22, the control device 42B functions as a ring movement control section 156, and is similar to the control device 42A of the second embodiment (see FIG. 15) except that the corneal curvature calculation method by the corneal curvature calculation section 114 is different. ) has basically the same configuration. When the corneal curvature of the subject's eye E is not measured, the corneal curvature calculator 114 may be omitted, as in the control device 42 (see FIG. 12) of the first embodiment.

The ring movement control unit 156 drives the actuator 150 to move the keratling light source 36 along the optical axis OA (vertical direction) in accordance with the position adjustment operation of the keratizing light source 36 input by the operator to the operation unit 96. Let This allows the actuator 150 to support the keratling light source 36 at any number of support positions different from the reference position. As a result, the size of the ring pattern 54 projected onto the cornea of the subject's eye E from the keratizing light source 36 can be adjusted more finely than in the above-described embodiments. Astigmatic information can be measured according to the pupil diameter.

The corneal curvature calculation unit 114 of the control device 42B acquires the captured image 40 for each position of the keratling light source 36 from the image acquisition unit 106, as in the above embodiments. Also, the corneal curvature calculator 114 acquires the position detection result of the keratling light source 36 from the linear position detection sensor 152 . Then, the corneal curvature calculator 114 calculates the corneal curvature of the subject's eye E based on the captured image 40 for each position of the keratling light source 36 and the position detection result of the linear position detection sensor 152 for each position of the keratling light source 36. Calculate.

Note that the astigmatism information calculation unit 108 of the control device 42B, based on the captured image 40 acquired for each position of the keratling light source 36 from the image acquisition unit 106, for each position of the kerating light source 36 (for each captured image 40) E astigmatism information is calculated.

[Modified Example of Microscope Body of First Embodiment]
FIG. 23 is a block diagram of a surgical microscope 10 having a microscope main body 26A that is a modification of the microscope main body 26 of the first embodiment.

The microscope main body 26 of the first embodiment includes an illumination optical system 60, an observation optical system 70, and a photographing optical system 80, but as shown in FIG. 23, the photographing optical system 80 is omitted from the microscope main body 26A. That is, the surgical microscope 10 having the microscope main body 26A is used only for observation of the cornea of the eye E by the operator. Except that the imaging optical system 80 is omitted and the control device 42 functions as the drive control section 100, the ring control section 102, and the optical system control section 104, the surgical microscope 10 is identical to the first embodiment. has basically the same configuration. For this reason, the same reference numerals are given to the same functions or configurations as those of the first embodiment, and the description thereof will be omitted.

Even with the surgical microscope 10 used only for observing the cornea of the subject's eye E, the operator can change the supporting position of the keratling light source 36 in the same manner as in the above-described embodiments. It is possible to change the size of the ring pattern 54 projected onto the cornea of the subject's eye E being observed through the . Accordingly, the operator can determine astigmatism information that matches the pupil diameter of the eye E to be examined by changing the size of the ring pattern 54 in accordance with the pupil diameter of the eye E to be examined.

Note that the surgical microscope 10 including the microscope main body 26A shown in FIG. 23 may be appropriately combined with one or more of the modified examples shown in FIGS. 19 to 22 described above. That is, the concentric ring pattern 54 is projected onto the cornea of the eye E to be inspected, the continuous ring pattern 54A is projected onto the cornea, and the position of the keratizing light source 36 is changed by the actuator 150. You may

[others]
In each of the above-described embodiments, the reference position, the first change position, and the second change position are provided as the support position of the keratling light source 36 by the keratling light source support section 38, so that the ring projected onto the cornea of the eye E to be examined Although the size of the pattern 54 can be changed in three steps, the number of support positions other than the retracted positions may be two or four or more. Thereby, the size of the ring pattern 54 projected onto the cornea of the eye E to be examined can be changed in two steps or in multiple steps of four steps or more.

In each of the above-described embodiments, the keratling light source 36 is provided at a position closer to the eye E than the microscope body 26, but conversely, the microscope body 26 is provided at a position closer to the eye E than the keratling light source 36. may be In each of the above-described embodiments, the optical axis OA of the microscope main body 26 and the projection axis PA of the keratling light source 36 are on the same straight line, but the optical axis OA and the projection axis PA may not be on the same straight line or may not be on the same straight line. They may be parallel. That is, if the projection of the ring pattern 54 or the like onto the cornea of the eye E to be examined by the keratling light source 36 and the imaging of the cornea by the microscope main body 26 are possible, the positional relationship between the keratizing light source 36 and the microscope main body 26 is particularly limited. is not done.

In each of the above embodiments, the ring patterns 54 and 54A are projected from the keratizing light source 36 onto the cornea of the eye E to be examined. The pattern may be projected onto the cornea of the eye E to be examined.

In each of the above embodiments, the surgical microscope 10 used for cataract surgery has been described as an example. The present invention can also be applied to an ophthalmic device that

10 Operational microscope 26, 26A Microscope body 32 Eyepiece 34 Photographing units 36, 36A, 36B Keratling light source 36a Supported parts 38, 38A Keratling light source support 39 Button type detection sensor 40 Photographed image 40A Reference position image 40B First change position image 40C Second change position images 42, 42A, 42B Control device 46 Opening hole 48 LED
54, 54A Ring pattern 58 Objective lens 60 Illumination optical system 61 Illumination light source 70 Observation optical system 80 Photographing optical system 83 Image sensor 90 Guide 92 Bolt 96 Operation unit 98 Storage unit 100 Drive Control unit 102 Ring control unit 104 Optical system control unit 106 Image acquisition unit 108 Astigmatism information calculation unit 110 Display control unit 112 Notification control unit 113 Index 114 Corneal curvature calculation unit 116 Positional relationship information 150 Actuator 152 Linear position detection sensor 154 Scale 156 Ring movement controller OA Optical axis PA Projection axis WD Working distance d Light source distance

Claims (7)

a projection light source that projects a measurement pattern onto the cornea of an eye to be inspected;
an imaging device for imaging the cornea on which the measurement pattern is projected by the projection light source;
The projection light source is supported at a plurality of supporting positions along the projection axis of the projection light source and is predetermined based on a reference value of the distance between the eye to be inspected and the projection light source; a support for selectively supporting at a plurality of support positions comprising one or more change positions different from
with
the imaging device imaging the cornea on which the measurement pattern is projected from the projection light source supported at the changed position by the support ;
the projection light source projects a continuous or intermittent ring pattern onto the cornea as the measurement pattern;
an astigmatism information calculation unit that calculates astigmatism information of the eye to be examined based on the captured image of the cornea captured by the imaging device;
the support section sequentially supports the projection light source at two or more of the plurality of support positions;
the imaging device imaging the cornea on which the ring pattern is projected from the projection light source at each of the two or more positions;
The astigmatism information calculation unit is an ophthalmologic apparatus in which the astigmatism information is calculated for each of the two or more positions based on the captured images captured by the imaging device for each of the two or more positions. The projection axis and the optical axis of the imaging device are on the same straight line,
the projection light source has an aperture through which the optical axis passes;
2. The ophthalmologic apparatus according to claim 1, wherein the photographing device photographs the cornea on which the measurement pattern is projected through the aperture. The support part is
a linear guide provided in the photographing device and extending in a direction parallel to the optical axis, the guide supporting the projection light source movably along the optical axis;
a fixing member for selectively releasably fixing the projection light source to the guide at the plurality of support positions;
3. The ophthalmic device of claim 2, comprising: The support part is
a linear guide provided in the photographing device and extending in a direction parallel to the optical axis, the guide supporting the projection light source movably along the optical axis;
an actuator for moving the projection light source along the guide;
3. The ophthalmic device of claim 2, comprising: The support unit is capable of supporting the projection light source at a retracted position, which is one of the plurality of support positions and is closer to the imaging device than the reference position and the changed position,
a detection unit that detects whether the projection light source is supported by the support unit at the retracted position;
Based on the detection result of the detection unit, when the support unit supports the projection light source at the retracted position, the projection light source is extinguished and the projection light source is supported at a position different from the retracted position. a light source control unit that turns on the projection light source when the
An ophthalmic device according to any one of claims 2 to 4, comprising: the projection light source projects a continuous or intermittent ring pattern onto the cornea as the measurement pattern;
the support section sequentially supports the projection light source at two or more of the plurality of support positions;
the imaging device imaging the cornea on which the ring pattern is projected from the projection light source at each of the two or more positions;
a relative position acquisition unit that acquires the relative position of the changed position with respect to the reference position;
A corneal curvature calculator for calculating the corneal curvature of the eye to be inspected based on the photographed images of the cornea photographed at each of the two or more positions by the photographing device and the relative positions obtained by the relative position obtaining unit. and,
An ophthalmic device according to any one of claims 1 to 5 , comprising: The ophthalmologic apparatus according to any one of claims 1 to 6 , wherein the projection light source projects a plurality of concentric ring patterns onto the cornea.

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