JP2763585B2 - Apparatus for determining anterior chamber depth of surgical eye and test lens apparatus used for determining the anterior chamber depth - Google Patents

Description

The present invention relates to an anterior chamber of a surgical eye for quickly determining an anterior chamber depth of an intraocular lens (IOL) inserted into a surgical eye from which a lens nucleus has been removed. The present invention relates to a depth determining device and a test lens device used for determining an anterior chamber depth.

(Prior Art) Conventionally, there is a technique of incising a cornea of a surgical eye to cut off a lens nucleus and inserting an intraocular lens having a predetermined power into the surgical eye for surgery on a cataract patient. To determine the power of the intraocular lens, for example, Bink shown below
There is one that uses horst formula.

P = 1000N (4R-L) / (LC) (4RC) Here, P is the power (power of the intraocular lens) of the intraocular lens in the anterior aqueous humor necessary for emmetropia. Ocular length (unit: mm), R: corneal curvature radius (unit: mm) measured by corneal curvature measuring means (keratometer), N: refractive index of anterior chamber and vitreous body, C: anterior chamber depth after operation (Depth of the anterior chamber). Here, as the anterior chamber depth C, a value corrected by the axial length L is used, but it is generally determined as a fixed value.

(Problems to be Solved by the Invention) By optical examination, if the insertion position of the intraocular lens in the direction of the eye is shifted by 1 mm, an error of about 1 diopter occurs as a refractive power value of the entire surgical eye. Therefore, even if the power of the intraocular lens can be determined precisely, there is a problem that the accuracy of the refractive power value of the surgical eye decreases due to the variation of the anterior chamber depth.

It is also conceivable to measure the anterior chamber depth by a conventionally used ultrasonic measurement method, but since the anterior position of the crystalline lens and the anterior position of the intraocular lens do not always match, it is based on the variation of the anterior chamber depth. It is difficult to suppress a decrease in the accuracy of the eye refractive power value. Furthermore, it is also difficult to reduce the dispersion of the measured values themselves by the ultrasonic measurement method.

Therefore, an object of the present invention is to provide a device for determining an anterior chamber depth of a surgical eye that can easily and accurately determine an anterior chamber depth of an intraocular lens inserted into a surgical eye from which a lens nucleus has been removed, and an anterior chamber depth determination thereof. A test lens device to be used is provided.

(Means for Solving the Problems) The apparatus for determining an anterior chamber depth of a surgical eye according to claim 1 of the present specification is an optical system corresponding to optical data of an intraocular lens inserted into the surgical eye. An eye-refractive-power measuring means for inserting a test lens having data into the surgical eye and measuring an eye refractive power of the surgical eye into which the test lens has been inserted; and an eye refraction measured with the test lens inserted. Calculating means for calculating an anterior chamber depth when the intraocular lens is inserted based on a force.

A test lens device used for determining an anterior chamber depth according to claim 2 of the present specification holds a test lens having optical data corresponding to optical data of an intraocular lens inserted into a surgical eye. There is provided a test lens holding means and a driving means for driving the test lens holding means so that the test lens is moved in the direction of the eye axis.

(Operation) The apparatus for determining an anterior chamber depth of a surgical eye according to the present invention inserts a test lens having optical data corresponding to optical data of an intraocular lens inserted into the surgical eye into the surgical eye, and inserts the test lens. The eye refractive power of the operated surgical eye is measured. Then, the depth of the anterior chamber when the intraocular lens is inserted is calculated based on the eye refractive power measured with the test lens inserted. Therefore, if the intraocular lens is inserted so as to have the anterior chamber depth, it is possible to suppress a decrease in the accuracy of the eye refractive power value due to the variation in the anterior chamber depth of the surgical eye.

Further, since the test lens device used in the anterior chamber depth determination device is configured to be movable in the axial direction of the surgical eye, it is possible to easily measure the refractive power of the surgical eye when inserting the test lens. it can.

In addition, this test lens is prepared corresponding to the type of the intraocular lens to be inserted.

(Example) Hereinafter, an anterior chamber depth determining apparatus according to the present invention and a test lens apparatus used for determining the anterior chamber depth will be described.

In order to determine the power of the intraocular lens, measurement of the axial length of the eye, measurement of the corneal curvature radius, and measurement of the refractive power of the eye can be used as conventional methods. Let us determine the power of the lens.

(Configuration of Intraocular Lens Power Determining Device) FIG. 1 shows an optical configuration of a power determining device according to the present invention. In FIG. 1, reference numeral 1 denotes a surgical eye, 2 denotes an anterior segment illumination optical system, and 3 denotes observation. An optical system 4 is an optical system for measuring an eye refractive power, and 5 is an optical system for measuring a corneal curvature radius. The anterior segment illumination optical system 2 is roughly composed of an anterior segment illumination light source 6, a condenser lens 7, and a prism 8 with a lens. The eye 1 'is illuminated. The observation optical system 3 has a mirror 10, relay lenses 11, 12, 13 and an eyepiece 14 together with the objective lens 9, and the operator observes the surgical eye 1 with the observation optical system 3. In FIG. 1, reference numeral 15 denotes an operator's eye.

The eye refractive power measuring optical system 4 includes a projection chart illumination light source 16, a projection chart 17, a beam splitter 18, a relay lens 19,
The projection chart includes a diaphragm 20, a relay lens 21, a light receiving mask 22, and a light receiving element 23. The projection chart light beam is reflected by the beam splitter 18, and passes through the relay lens 19, the diaphragm 20, the relay lens 21, the mirror 10, and the objective lens 9. Is projected on the fundus 24 of the surgical eye 1. The reflected light from the fundus 24 is guided to the mirror 10 via the objective lens 9 and is reflected by the mirror 10 so that the relay lens 21, the diaphragm 20, the relay lens 1
9. The light passes through the beam splitter 18 and the light receiving mask 22 and is guided to the light receiving element 23. A projection chart illumination light source 16 and the projection chart 17 is movable in the arrow X ₁ direction, light mask 22 and the light receiving element 23 is movable in direction of arrow X _2, the moving amount of the light receiving element 23 is potention The output of the potentiometer 25 is detected by the meter 25, and the output of the potentiometer 25 is input to the measuring circuit 26. Based on the output of the potentiometer 25, the eye refractive power of the surgical eye 1 is measured.

The corneal curvature radius measuring optical system 5 includes an illumination light source 27, a mirror 28,
A surgical lens 1 comprising a projection lens 29 and a solid-state image sensor 30
Are illuminated by the illumination light source 27, and a ring-shaped virtual image is formed on the cornea 31. The corneal reflected light forming the ring-shaped virtual image is reflected by the mirror 28, and an image corresponding to the ring-shaped virtual image is formed on the solid-state imaging device 30 by the projection lens 29,
The output of the solid-state imaging device 30 is input to the measurement circuit 26, and the corneal curvature radius is measured. These measuring optics are built into the surgical microscope.

As shown in FIG. 2, the measuring circuit 26 has a corneal curvature radius input means 32 and an eye refractive power measurement value input means 33, and a desired eye refractive power value for inputting a desired expected eye refractive power value after the operation. Input means 34, optical data input means 35 for inputting predetermined optical data, and arithmetic means 36 are provided. This optical data will be described later. The calculating means 36 calculates the eye axis length based on the corneal curvature radius input means 32, the eye refractive power measurement value input means 33, the scheduled eye refractive power value input means 34, and the optical data input means, and calculates the axial length. It has a function as an axial length calculating means for recording and displaying, and a function as a power determining means for calculating the power of the intraocular lens based on the calculated axial length and a desired expected eye refractive power value after the operation.

The measurement circuit 26 calculates the axial length based on the corneal curvature radius value and the measured ocular refractive power, the axial length calculating means 31 for displaying and recording the calculated axial length, and the calculated axial length. Power determining means for calculating the power of the intraocular lens of the surgical eye 1 based on the desired eye refractive power value after the operation.

Before describing the procedure for calculating the axial length and the procedure for determining the power of the intraocular lens based on the flowchart, the optical data required will be described with reference to FIGS. 3 and 4. FIG.

FIG. 3 is a schematic view of the surgical eye 1 on which the contact lens 37 is worn, and FIG. 4 is a schematic view of the surgical eye 1 on which the intraocular lens 38 is set. The third diagram in Figure 4, r ₁ a front radius of curvature of the contact lens 37, the rear surface radius of curvature r _2, d ₁ and its thickness, the refractive index n _2, tear 39
Is the thickness of d ₂ , its refractive index is n ₃ , the corneal curvature radius of the anterior corneal surface of the cornea 31 is r ₃ , its posterior corneal curvature radius is r ₄ , its thickness is d ₃ , and its refractive index is n ₄ The thickness of the anterior chamber 40 is d ₅ , its refractive index is n ₅ , the radius of curvature of the front surface of the intraocular lens 38 is r ₅ , then both the radii of curvature are r ₆ , its thickness is n ₆ , and the thickness of the vitreous body 41 Let d _{7 be} the refractive index and n ₇ the refractive index. Here, n ₁ is the refractive index in air.

Corneal curvature radius r ₃ is determined by measuring the value of the r ₃ is generally 6.9Mm～8.5Mm. Also, the corneal radius of curvature r ₄ is assumed to 6.8mm by reference to literature. The radii of curvature r ₁ and r _{2 of} the contact lens 37, the thickness d ₁ , the thickness d _{6 of} the intraocular lens 38, the refractive index n ₂ of the contact and the lens 37, the intraocular lens 38
The refractive index n _{6 of} is determined by the specification, and r ₁ ≒ r ₂ ≒
r ₃ , d ₁ = 0.2, d ₆ = 1.0, and n ₂ = n ₆ = 1.491. Further, the thickness d ₂ of the tear 39, the thickness d _{3 of} the cornea 31, the inter-plane distance d ₅ from the posterior surface of the cornea 31 to the anterior surface of the lens nucleus (the intraocular lens 38),
Refractive index of air n _1, the refractive index n ₃ of the tear 39, the refractive index of the cornea 31
n ₄ and the refractive index n ₅ of the anterior chamber 40 are determined as follows with reference to literatures and the like.

d ₂ = 0.1, d ₃ = 0.5, d ₅ = 3.6, n ₁ = 1.0, n ₃ = n ₅ == 1.33
6, n ₄ = 1.376, n ₇ = n ₅ , and r ₆ = ∞. These optical data are input by optical data input means.

The radius of curvature r ₅ of the front surface of the intraocular lens 38, the intraocular lens 38
The inter-plane distance d ₇ from the posterior surface of the cornea 31 to the image point O ′ and the inter-plane distance d ₄ from the posterior surface of the cornea 31 to the image point O ′ are calculated by the calculating means 36.

These calculations are performed by paraxial calculation.
As shown in the figure, tracing of paraxial rays of an optical system generally consisting of a spherical series of k refracting surfaces will be considered. In FIG. 5, S is the optical axis distance from the object point O to the first surface, S 'is the optical axis distance from the Kth surface to the image point, O', dν '
Is the inter-surface region between the ν-th refractive surface and the ν + 1-th refractive surface (the thickness of the lens between the ν-th refractive surface and the ν + 1-th refractive surface), and Nν ′ = Nν _{+ 1} is the ν-th refractive surface. Ν + 1
Hν is the height from the optical axis at the νth refraction surface, and U ₁ is the _first refraction from the object point O
The inclination angle U _{k + 1} of the ray incident on the surface at the height h ₁ with respect to the optical axis is the image point O ′ emitted from the k-th surface at the height h _k
Angles of light rays incident on the optical axis with respect to the optical axis, Uν ′, Uν _{+ 1}
Is the inclination angle of the light ray incident on the ν + 1-th refracting surface with respect to the optical axis, and rν is the radius of curvature of the ν-th refracting surface.

 Then, the following equation generally holds.

Nν ′ · Uν ′ = Nν + Uν + ｛(Nν−Nν ′) · h
ν｝ / rν Nν ′ = Nν ₊₁ Uν ₊₁ = Uν ′ hν ₊₁ = hν−dν ′ · Uν ′ Nν _{+ 1} · Uν ₊₁ = Nν · Uν + ｛(Nν ₊₁ −Nν) · h
ν｝ / rν hν ₊₁ = hν−dν′Uν ₊₁ where S = h ₁ / U ₁ = 1 / U ₁ h ₁ is an arbitrary value, but here, h ₁ =
It was set to 1.

S ′ = h _k / U _{k + 1} Note that when S is expressed in diopters, S = −1000 / D ₁ . Here, the desired scheduled eye refractive power value after D ₁ surgery.

Here, when tracing a ray from the object point O, the optical axis distance S from the image point O to the first surface is determined. When tracing a ray from the image point O ', the object point O' from the k-th surface. The optical axis distance S 'is determined. In FIG. 5, the surface closest to the object point O is defined as the first surface, but ray tracing may be performed with the surface closest to the image point O 'as the first surface.

Hereinafter, a method for determining the power of the intraocular lens 38 will be described with reference to the drawings.

(Calculation Procedure of Ocular Axial Length) First, as shown in FIG. 6, a corneal curvature radius r ₃ is obtained and recorded before the incision of the surgical eye 1 by the corneal curvature radius measuring optical system 5 as a corneal curvature radius measuring means. (S1). And
The surgical eye 1 is incised and the lens nucleus 24 'is resected (S2).
The contact lens 37 is worn on the surgical eye 1, which is the aphakic eye from which the lens nucleus 24 'has been removed (S3). Next, the lens nucleus
The eye refractive power of the surgical eye 1 from which 24 'has been removed and the contact lens 37 is worn is measured by the eye refractive power measuring optical system 4 as eye refractive power measuring means (S4). As a result, the eye refractive power is obtained by adding the eye refractive power of the contact lens 37 to the eye refractive power of the surgical eye 1 from which the lens nucleus 24 'has been removed.

Next, the distance between the object plane O conjugated to the fundus oculi 24 and the vertex P of the contact lens 37 based on the eye refractive power value in the eye axis direction
To calculate the S ₀ (S5). Based on the paraxial calculation formula described above,
The position of the image point O 'with respect to the object plane O is calculated (S6). Then, the arithmetic unit 36 calculates the inter-plane distance d ₄ from the position of the image point O 'to the rear surface of the cornea 31 (S7), and calculates a d ₃ + d ₄ using this value as the axial length L (S8 ).

(Procedure for Determining Power of Intraocular Lens) A desired expected eye refractive power value D1 after the insertion of the intraocular lens 38 into the surgical eye ₁ is determined (S1). Then, to calculate the interplanar distance d ₇ to the image point O 'from the rear surface of the intraocular lens 38 on the basis of the interplanar distance d ₄ obtained in S7 of the eye axial length measurement procedure (S2). And the fundus
The inter-plane distance S ₁ between the image plane O ₁ conjugated to 24 and the vertex position of the cornea 31 of the surgical eye 1 is obtained by the following equation S ₁ = (− 1000) / D ₁ (S 3).

Next, the power of the intraocular lens 38 is temporarily set to P '. Then, the inter-plane distance S ₁ ′ from the surgical eye 1 to the image point is obtained using the above-described paraxial calculation formula. The diopter display of the inter-plane distance S ₁ ′ is set to D ₁ ′ = (− 1000) / S ₁ ′ (S 4).

Then, in S5, it is determined whether or not | D ₁ −D ₁ ′ | <0.1. When S5 is NO, P '
= P '+ 0.1, and D ₁ ' is newly obtained. The newly obtained D ₁ ′ is defined as D ₂ ′ (S6). Then, in S7, it is determined whether or not | D ₁ −D ₂ ′ | <0.1.

In S7, if NO, the process proceeds to S8, where | D ₁ −D ₁ ′
It is determined whether or not |> | D ₁ −D ₂ ′ |. If YES in S8, the process proceeds to S6, where the processing of P '= P' + 0.1 is performed again to newly obtain D ₁ '. This newly sought
Let D ₁ ′ be D ₂ ′. By repeating the processes of S6 to S8, the power of the intraocular lens 38 is updated by 0.1.

When S8 is No, P '= P'-0.1,
D ₁ 'is obtained (S9). Then, the flow shifts to S10, where | D ₁ −D
_It is determined whether ₁ ′ | <0.1. When NO at S10, 'a _{= P'-0.1, D 1'} P goes to S9 again seek to repeat the process. In S10, when YES, the power of the intraocular lens 38 to achieve the desired ocular refractive power D ₁ ends the process as P = P '(S11).

In S5, S7, power of the intraocular lens 38 to achieve the desired eye refractive power D ₁ also when yes, the process ends as P = P '(S11). Therefore, by repeating this processing, the power P of the intraocular lens 38 can be determined with an accuracy of 0.1.

According to this embodiment, if a contact lens 37 having a positive power is used for the surgical eye 1, the power of the surgical eye 1 after the removal of the lens nucleus 24 'is negative, and therefore the contact lens 37 It is convenient to measure the refractive power of the eye while wearing the lens, because it is close to zero diopter.

In the paraxial calculation in this power determination procedure,
Instead of entering the power of the intraocular lens 38 to enter the radius of curvature r ₅ of the intraocular lens 38 as a variable. This radius of curvature
If by changing the r ₅ and to perform the paraxial calculation, the variation [Delta] P = 0.01 power P variation [Delta] r ₅ of the radius of curvature r _5, [Delta] r ₅ =
Equivalent to 0.005.

Here, the intraocular lens 38 having the power obtained through such a procedure is inserted into the surgical eye 1.
In order to determine the insertion position of the intraocular lens 38, FIG.
The anterior chamber depth is measured using the test lens device shown in FIG.

FIG. 8 is a view showing a first embodiment of a test lens device used in the anterior chamber depth determining device according to the present invention. In FIG. 8, reference numeral 50 denotes a fixed cylinder constituting the test lens device. The fixed barrel 50 is provided with a movable barrel 51.
A screw portion 52 is provided at the bottom of the moving cylinder 51, and the screw portion 52 is screwed to an inner peripheral portion of a rotating cylinder 53 rotatably attached to the fixed cylinder 50. A spring wire 54 is attached to the tip of the moving cylinder 51, and the spring wire
A test lens 55 shown in FIG. Here, the movable cylinder 51 and the spring wire 54 function as holding means for holding the test lens 55.

A pin 56 is implanted around the moving cylinder 51, and the pin 56 projects outside the fixed cylinder 50 through a slit 57 formed in the longitudinal direction of the fixed cylinder 50. The moving cylinder 51 is reciprocated in the vertical direction when the rotating cylinder 53 is rotated, and the wire spring 54 is reciprocated in the direction of the arrow with the reciprocating movement of the moving cylinder 51,
When the depth of the anterior chamber is determined, the position of the test lens 55 in the direction of the eye axis is adjusted. Here, the rotating cylinder 53 functions as a driving unit that drives the test lens holding unit. pin
Reference numeral 56 has a function of displaying the position of the test lens 55 from the reference position, and an indication scale is formed on the outer peripheral portion of the fixed cylinder 50 along the direction in which the slit 57 extends. Note that 5
Reference numeral 3 'denotes a knob formed on the rotary cylinder 53.

FIG. 9 is a view showing a second embodiment of the test lens device. In FIG. 9, reference numeral 60 denotes a fixed tube, and a hollow tube 61 is provided in the fixed tube 60 in a vertical direction. At the lower end of the hollow cylinder 61, an injection tube 62 extending in the lateral direction is provided, and at the upper end of the hollow cylinder 61, a balloon 63 constituting test lens holding means and a test lens is provided. The balloon 63 is filled with a silicone fluid 64 via an injection tube 62 and a hollow cylinder 61, and the injection tube 62 is filled with a syringe.
64 'is inserted and the silicon fluid 64 is injected.
When the balloon 63 is filled with the silicon fluid 64, it expands to form the test lens 55 as shown in FIG.

These test lenses 55 are inserted into the surgical eye 1 from which the lens nucleus 24 'has been removed as shown in FIG. 12, and the depth of the anterior chamber is determined. Various types are prepared in accordance with the optical data.

(Procedure for Determining Anterior Chamber Depth) First, as shown in FIG. 13, the test lens 55 is inserted into the surgical eye 1 from which the lens nucleus 24 ′ has been removed, and
While wearing contact lenses, measures the eye refractive power D ₀ of the operating eye 1. Here, for measuring the eye refractive power D ₀ by wearing contact lenses, corneal incision, for example, because astigmatism, distortion occurs even incision has healed. Here, the eye refractive power measuring optical system 4 is used for this measurement. Then, according to the flowchart shown in FIG. 14, the eye refractive power D ₀ , the axial length L = d ₃ + d ₄ , r _{1 to} r ₆ , d _{1 to} d ₄ , and n _{1 to} n ₇ are input to the calculating means 36. (S1). Here, r ₅ , r ₆ , d ₅ , and n ₆ are optical data of the test lens 55, and here, the eye axis length L and the corneal curvature radius r ₃ are measured values obtained in the eye axis length measurement procedure. Used. Next, the calculating means 36
Then, the calculation of S ₀ = −1000 / D ₀ is performed (S2).

And, temporarily, the anterior chamber depth is set to d _50, and the true anterior chamber depth is d.
As _5, and _{d 5 = d 50 (S3)} . Then, the value of d ₇ determined using the following formula (S4).

_{d 7 = L- (d 3 +} d 5 + d 6).

Then, a subroutine process paraxial calculation, obtaining the fundus 24 a conjugate position S ₁ was measured with the intraocular lens 38 (S5). Next, the absolute value of the difference between S ₁ and S ₀ and goes to S6 |
It is determined whether S ₁ −S ₀ | <0.05. If the answer is NO in S6, the process proceeds to S7, and it is determined whether S ₁ −S ₀ > 0.

When yes in step S7 proceeds to _{S8, d 5 = d 5 -0} .
The arithmetic processing of 01 is performed, and the processing of S4 to S8 is repeated. This makes it possible to be subject to the values of anterior chamber depth d ₅₀ of the provisional by 0.01 to approach the true anterior chamber depth d _5. In S7, if no, the process proceeds to S9, where the processing of d ₅ = d ₅ +0.01 is performed,
Steps S4 to S7 and S9 are repeated. This makes it possible to be subtracted value of anterior chamber depth d ₅₀ of the provisional by 0.01 to approach the true anterior chamber depth d _5. When the difference between the fundus 24 and conjugate position S ₁ and S ₀ is within 0.05, it is determined YES in S6,
S10 is chamber depth d ₅ before it proceeds is printed out. In this way, the true anterior chamber depth is determined with an accuracy of 0.01 mm.

A series of these processes is performed by the measurement circuit 26. The measurement circuit 26 cooperates with the optical system to apply a test lens having optical data corresponding to the optical data of the intraocular lens inserted into the surgical eye to the surgical eye. An intraocular lens was inserted based on the role as an eye-refractive-power measuring means for measuring the eye-refractive power of the surgical eye in which the test lens was inserted and the eye was measured with the test lens inserted. At the time of the anterior chamber depth.

(Effect of the Invention) According to the apparatus for determining an anterior chamber depth of a surgical eye according to the present invention,
The depth of the anterior chamber of the intraocular lens inserted into the surgical eye from which the lens nucleus has been removed can be easily and accurately determined. Therefore, it is possible to expect an improvement in the operation results of cataract.

ADVANTAGE OF THE INVENTION According to the test lens apparatus used for the anterior chamber depth determination apparatus which concerns on this invention, the position adjustment of the test lens in the axial direction at the time of anterior chamber depth measurement can be performed easily.

[Brief description of the drawings]

FIG. 1 is a diagram showing a schematic configuration of an optical system of a device for determining the power of an intraocular lens according to the present invention, FIG. 2 is a block diagram showing a detailed configuration of a measurement circuit shown in FIG. 1, and FIG. FIG. 4 is a schematic view of the surgical eye 1 in which an intraocular lens is set, FIG. 5 is an explanatory view used for explaining paraxial calculation, and FIG. 6 is an axial length. FIG. 7 is a flowchart of a measurement procedure, and FIG. 7 is a flowchart of a power determination procedure. FIG. 8 is a diagram showing a first embodiment of a test lens device used in the anterior chamber depth determining apparatus according to the present invention, and FIG. 9 is a second example of the test lens device used in the anterior chamber depth determining method according to the present invention. FIG. 10 is a view showing an embodiment, FIG. 10 is a front view of the test lens shown in FIG. 8, FIG. 11 is a front view of the test lens shown in FIG. 9, and FIG. FIG. 13 is a schematic view of a surgical eye wearing a contact lens and a test lens. FIG. 14 is a flowchart showing an anterior chamber depth determination procedure according to the present invention. Measurement optical system 5: corneal curvature radius measurement optical system, 24: fundus 24 '... lens nucleus, 26 ... measurement circuit 31 ... cornea, 37 ... contact lens 38 ... intraocular lens, 51 ... moving cylinder 53 ... rotating cylinder, 54 ... Spring wire 55… Test lens, 63… Balloon

──────────────────────────────────────────────────続 き Continued on the front page (72) Inventor Hiroshi Uosato 840 Shijo-cho, Kashihara City, Nara Prefecture Nara Prefectural University of Medical Science (58) Field surveyed (Int. Cl. ⁶ , DB name) A61B 3/00

Claims (2)

(57) [Claims] An eye for inserting a test lens having optical data corresponding to optical data of an intraocular lens inserted into a surgical eye into the surgical eye and measuring an eye refractive power of the surgical eye into which the test lens is inserted. Surgery comprising: refractive power measuring means; and calculating means for calculating an anterior chamber depth when the intraocular lens is inserted based on the eye refractive power measured with the test lens inserted. An anterior chamber depth determining device for the eye. 2. A test lens holding means for holding a test lens having optical data corresponding to the optical data of an intraocular lens inserted into a surgical eye, and the test lens is moved by the test lens in the direction of the eye axis. A test lens device for determining an anterior chamber depth, comprising: a driving unit for driving the test lens.