JP6943523B2 - Eye device - Google Patents

Description

The present invention relates to an eye device, particularly an eye device for improving visual acuity (depth), which is used for an eyeball in which the accommodation function of the focal point inherent in the crystalline lens is deteriorated. The present invention also relates to an ocular device used to predict postoperative visual function before cataract surgery.

In the treatment of cataracts, ocular lenses have been put into practical use as a substitute for the crystalline lens in order to replace the human opaque crystalline lens and correct the refraction. Conventionally, patients who have undergone the above-mentioned cataract treatment have undergone an operation to insert an intraocular lens, which is an artificial crystalline lens, into the crystalline lens by wearing glasses or contact lenses having so-called positive power. It supplements the refractive power of. There are various types of optical elements used for the above-mentioned cataract treatment, such as a single focus lens, an aspherical lens, a toric lens, and a multifocal lens.

When treating cataracts, generally by replacing the intraocular lens, the accommodation function of the patient's crystalline lens is lost. Therefore, an excellent field of view can be obtained at a certain focus position, but the image is deteriorated at other focus positions. That is, the depth of field becomes narrow. As a result, for example, a situation may occur in which a person cannot read because he / she can see in the distance but cannot see in the near area.

In recent years, multifocal lenses and accommodative lenses have been provided as intraocular lenses to deal with the problem of loss of accommodation power of the focal point of the eyeball after cataract surgery, but both still have many problems and are the best. It is not a cure for cataract surgery.

In this adjustable intraocular lens, the distance between a lens having a positive power and a lens having a negative power is changed by the ciliary muscle, or the radius of curvature of the lens is changed. As a result, the focal length of the lens changes. There are also intraocular lenses that detect the amount of light taken into the eye according to the size of the pupil of the patient and change the accommodation power, and spectacles that use a liquid lens that can change the power. However, for accommodative lenses, the mechanism for obtaining sufficient focal accommodation power in the narrow area of the eye has not been established, and it is still in the research stage.

On the other hand, multifocal lenses have already been adopted in cataract surgery, but most multifocal lenses are designed so that only two points, far and near, can be seen, and the image quality deteriorates in the middle region. There are many. Even if it is visible, the contrast is inferior to that of a healthy person because there is always light different from the light that forms the image.

However, there is a fact that the number of patients undergoing surgery after accepting the above-mentioned problems by fully explaining the above-mentioned problems to patients before cataract surgery is increasing. However, since the visual field provided by the multifocal lens looks different from the human visual function, it is difficult to imagine the postoperative visual field no matter how much it is explained to the patient before surgery, so it is necessary for postoperative trials. It often develops.

On the other hand, if the patient can experience the field of view when the multifocal lens is replaced with the crystalline lens before surgery, the advantages of the multifocal lens can be fully utilized, the burden on the doctor can be reduced, and the patient can feel at ease. I think I can have surgery.

International Publication No. 2015/040957 Patent No. 541905 Japanese Unexamined Patent Publication No. 10-253898 Japanese Unexamined Patent Publication No. 10-144975

The technique disclosed in the present case was made in view of the above circumstances, and the problem is that the lens is covered in an eyeball in which the accommodation function of the focal point originally possessed by the crystalline lens is deteriorated due to the fact that the crystalline lens is absent due to surgery or the like. The purpose of the present invention is to provide an eye device capable of improving the depth of field and improving the visual function. It is also an eye device that allows a patient to experience the field of view when a multifocal lens is inserted before cataract surgery.

The present invention for solving the above problems is an optical system that realizes a human visual function, and includes an optical system whose focal length changes depending on eyeglasses, contact lenses, IOLs, or other devices (hereinafter, includes an eyeball). An ophthalmic device having an element that changes the focal length of the optical system) at intervals shorter than the time resolution of the eyeball.
The element is characterized in that the focal length of the optical system including the eyeball is changed so as to be uneven in time in the variable range of the focal length.

That is, the ophthalmic apparatus disclosed in the present disclosure includes an element that changes the focal length of the optical system including the eyeball at a time interval shorter than the time resolution of the eyeball. As a result, the wearer of the ophthalmic device can transmit an in-focus image to the brain over a range from a distance to a near portion even when the adjusting force of the crystalline lens is deteriorated. In the present invention, the deterioration of the accommodative function (accommodative force) of the crystalline lens means that the accommodative function (accommodative force) of the crystalline lens is completely lost due to the absence of the crystalline lens due to surgery or the like, and the reason for aging, illness, etc. This includes cases where the accommodation function (accommodation power) of the crystalline lens is weakened due to this. Further, in the optical system including the eyeball of the present invention, even if the element whose focal length changes is a device such as spectacles, a contact lens, or an IOL, the eyeball component (cornea, crystalline lens) affected by the device or other device. , Aqueous humor, vitreous body, axial length, etc.).

Further, in the present invention, in the variable range of the focal length, the time when the focal length of the optical system including the eyeball becomes a predetermined first focal length is the time when the focal length is the first focal length. The focal length of the optical system including the eyeball may be changed so as to be longer than the time for which the second focal length is different.

That is, the present invention makes the time of being in a state of a certain focal length different from the time of being in a state of another focal length in a variable range that can be changed when the focal length is changed. According to this, it is possible to improve the visual acuity of the object near the first focal length more than the visual acuity of the object near the second focal length, and the visual function after wearing the eye device has a higher degree of freedom. It is possible to set with.

For example, when an element that can change the focus position from 5 m to 50 cm by changing the focal length is used, and the time to change the focus from 5 m to 50 cm is faster than the time resolution of the eyeball, the focus is 5 m. When the time when the image is in focus is made longer than the time when the image is in focus at 50 cm, the image quality of 5 m is better than the image quality of 50 cm. As another example, when changing from a focus position of 5 m to a focus position of 50 cm, it is possible to make it difficult to focus on anything other than 5 m and 50 cm by making a sudden change (for example, in a rectangular wave). can. These features can be used to experience preoperative field of view for a variety of multifocal lenses. When the focal length is changed by the element, it may be changed in a complicated cycle in consideration of the characteristics of multifocal length and the patient's request, instead of the monotonous periodicity. Further, the change waveform may be set according to the characteristics of the multifocal intraocular lens to be inserted.

Further, in the present invention, the change waveform when the element changes the focal length of the optical system including the eyeball may include any of a square wave, a triangular wave, a sine wave, and a trapezoidal wave. Depending on these waveforms or a combination thereof, it is possible to change the focal length in a variable range of the focal length so as to be uneven in time in various variations.

Further, in the present invention, the element sets the time during which the focal length of the optical system including the eyeball becomes a predetermined focal length in the variable range of the focal length according to the MTF required at the predetermined focal length. It may be determined by.

Further, in the present invention, the element changes the focal length of the optical system including the eyeball so as to be stopped for a predetermined time at each of a plurality of focal lengths in the variable range of the focal length. , Each of the plurality of focal lengths may be determined based on the ratio of MTF required for the optical system including the eyeball.

Here, in a multifocal lens, it is known that the MTF at each focal length depends on the amount of light focused on the focal length. Therefore, in the variable range of the focal length, the time during which the focal length of the optical system including the eyeball becomes a predetermined focal length is determined according to the MTF required at the predetermined focal length, thereby meeting the required specifications. It is possible to construct a multifocal lens system.

That is, in a general multifocal lens, the MTF at each focal length can be adjusted by appropriately setting the area of the lens surface having each focal length. However, in the present invention, the time for each focal length is set. With proper setting, the MTF at each focal length can be adjusted. Since this time can be changed in real time by appropriately controlling the operation of the element, in the present invention, it is also possible to adjust the focal length of the optical system including the eyeball in real time.

Further, in the present invention, the eye device may include a contact lens that comes into contact with the eyeball and constitutes a part of the optical system including the eyeball. Further, the eye device may include eyeglasses that form a part of an optical system including the eyeball in a state of being separated from the eyeball.

Further, the ophthalmic device may include a soft contact lens, and a tear film may be formed between the lens and the cornea of the eyeball. Alternatively, the drive source of the above-mentioned element may be a solar cell provided in the lens and having light transmission. Alternatively, the lens may be formed containing a piezoelectric substance having light transmission. Alternatively, the above lens may be an intraocular lens inserted after the iris of the eyeball.

Further, in the present invention, the ophthalmic apparatus may include an optometry lens worn by the patient before the operation of inserting the multifocal intraocular lens.

Here, as described above, most multifocal intraocular lenses are designed so that only two points, a distant point and a near point, can be seen, and the image quality often deteriorates in the intermediate region. In addition, the contrast is inferior to that of a healthy person. On the other hand, the number of patients undergoing surgery for multifocal intraocular lenses is increasing while allowing the above risks. However, it is difficult for the patient to accurately image the postoperative visual field, and the difference between the patient's image and the postoperative visual field may become a problem. The multifocal intraocular lens is not limited to two focal points, but may be three focal points, and is EDOF (Expanded Depth o).
It may be a depth-expanded type called f focus or Field), and it does not depend on the type of multifocal lens.

On the other hand, in the present invention, the above-mentioned ocular device is applied to an optometric lens worn by a patient before the insertion operation of the multifocal intraocular lens. According to this, the patient can experience the field of view when the multifocal intraocular lens is replaced with the crystalline lens before the operation. As a result, the patient's anxiety can be eliminated, and troubles can be prevented after the surgery due to the difference between the patient's image and the actual appearance after the surgery.

Further, in the present invention, the eye device may include a vibrating film that constitutes a part of the optical system including the eyeball. Further, the element in the present invention may change the focal length by any of electromagnetic force, voltage, current, ultrasonic wave or air pressure.

More specifically, the elements of the present invention include a lens that is inserted into an optical system including an eyeball and can electrically change the focal length, and a lens that applies electric power that changes with a predetermined increase / decrease range at the above time intervals. It may be configured to have a power supply unit for supplying power to the lens. Alternatively, the element may have an air injection unit that injects air into the cornea of the eyeball at the above time intervals. Alternatively, the element may have a configuration having an ultrasonic wave generating portion that generates ultrasonic waves radiated to the front surface of the cornea of the eyeball at the above time intervals.

The element may change only the focal length of the optical system including the eyeball of one eye. That is, the eye device according to the present invention may be applied to only one eye. Alternatively, while applying the ophthalmic apparatus of the present invention to both eyes, the focal length may not be changed for one eye and the focal length may be changed at high speed in the other eye. According to this, the effect of "Monovision" prescribed in the ophthalmology industry can be expected. That is, by applying a single-focus eye device to the dominant eye and applying the eye device according to the present invention to the other eye, a wide depth of field can be obtained while maintaining the influence on the brain waves related to vision. Is possible.

Further, in the present invention, the element may change the focal length of the optical system including the eyeballs of both eyes. Further, the state of change in the focal length in the eyeballs of both eyes may be the same. According to this, the patient can obtain higher visual function and can suppress feelings of discomfort and tiredness.

Further, in the present invention, the state of change in the focal length in the eyeballs of both eyes may be different. This also makes it possible to expect the effect of "monovision" and obtain a wide depth of field while maintaining the influence on the brain waves related to vision.

As another component, the ophthalmic device may be a medical device, such as a fundus camera with a chin rest. Further, in the present invention, it is more preferable that the size of the diaphragm can be adjusted at the time of adjustment. This is because when the focal length is changed, the closer the factor that changes the focal length is to the position of the aperture, the smaller the influence of the magnification and the better the image can be obtained. Therefore, it is advisable to make the aperture smaller than the pupil of the subject.

In the present invention, the means for solving the above-mentioned problems can be used in combination as much as possible.

According to the technique disclosed in the present case, it is possible to improve the depth of field and the visual function in an eyeball in which the accommodation function of the focal point originally possessed by the crystalline lens is deteriorated due to the absence of the crystalline lens due to surgery or the like. .. In addition, before cataract surgery, the patient can experience the field of view when the multifocal lens is inserted.

It is a figure which shows an example of the apparatus used for the experiment in this invention. It is a figure which shows an example of the apparatus used for the experiment in this invention. It is a figure which shows the drive waveform of the conventional ophthalmic apparatus. It is the first figure which shows the drive waveform of the eye apparatus in one Example. It is a second figure which shows the drive waveform of the ophthalmic apparatus in one Example. It is a third figure which shows the drive waveform of the ophthalmic apparatus in one Example. It is a figure which shows the MTF at each of the two focal lengths which the maintenance time of an ophthalmic apparatus is different in one Example. It is a 4th figure which shows the drive waveform of the eye apparatus in one Example. It is a 5th figure which shows the drive waveform of the eye apparatus in one Example. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one Example. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one Example. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one Example. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one Example. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one Example. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one modification. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one modification. It is a figure which illustrates the schematic structure of the ophthalmic apparatus in one modification.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.

It is known that the human eye constantly vibrates at a frequency of 30 to 150 Hz. This is thought to be because the focus can be quickly adjusted in any direction by vibrating the focal point. Further, a lighting fixture such as a fluorescent lamp blinks at a high speed according to the frequency of the supplied power supply, but the blinking is not detected by the human eye. That is, the image that vibrates at a frequency of 30 Hz or higher is recognized by the human brain as a continuously moving image, not as a vibrating image.

In addition, there is an image that utilizes the human illusion called a hybrid image. This combines an image drawn with only high frequency components, that is, an image that emphasizes the outline of the object in the image, and an image drawn with only low frequency components, that is, an image in which the outline of the object in the image is blurred. It is an image that was made. When an image with a blurred outline and an image with a conspicuous outline are superposed on each other, the image with a conspicuous outline is easily recognized by the human eye, and the image with a conspicuous outline is difficult to be recognized. That is, according to human visual function, if an image with a prominent contour is transmitted to the brain, it is considered that an image with a prominent contour is recognized even if there is an image with a blurred contour. ..

On the other hand, when the hybrid image is moved away from the eye, each minute element of the image drawn only with the high frequency component becomes blurred and difficult to see, and the element of the image drawn only with the low frequency component becomes more difficult to see. It becomes easier to see. That is, when an image that is in focus with an eyeball having a deteriorated accommodation function and an image that is out of focus closer to the image are viewed, the image that is in focus is easily recognized by the eye and is near. Blurred images are considered difficult to recognize.

Therefore, by fluctuating the focal length of the optical system including the eyeball at 30 Hz or higher, such as by applying a variable focus type optical element whose focus moves at a frequency of 30 Hz or higher to the eyeball whose adjustment function has deteriorated, the fluctuation range It is possible to focus on a plurality of focal lengths at the same time, and the brain recognizes that an image within the fluctuation range of the focal length is in focus. That is, even when the adjustment function of the eyeball is lost, by adopting the above configuration, it is possible to transmit an image in focus to the brain from near to far.

In the present embodiment, by fluctuating the focal length of the optical element at high speed, even if the adjustment function of the eyeball is deteriorated, it is possible to focus within a wide focal length range and to have a fixed focus. There is no intermediate region where the visual function deteriorates as in the case of using a multifocal lens, and problems such as halo and glare can be satisfactorily avoided. The specific configuration of the ophthalmic device according to this embodiment will be described later.

Next, a simulation is performed using the following experimental device to see what the image looks like when the focal length in the optical system including the eyeball fluctuates at high speed. In this embodiment, the experimental device 1 shown in FIG. 1 is used. First, two charts 10 and 20 on which different indexes are written are fixed to the vibration tester 30 at a distance of 2.3 mm from each other. The chart 10 is a quadrangular plate-shaped member having light transmission, and a grid figure is attached to each of the four corners of the chart 10. Further, the chart 20 is also a quadrangular plate-shaped member having light transmission, and a grid figure is attached near the center of the chart 20. It is assumed that the sizes of the charts 10 and 20 are the same as each other. Here, the vibration tester 30 is a device capable of vibrating the charts 10 and 20 at a frequency of 50 Hz or higher. In FIG. 1, the lattice figures attached to the charts 10 and 20 are shown as the same pattern.

A light source 40 is installed in front of the charts 10 and 20. The light source 40 has a halogen lamp 40a and a condenser lens 40b as an example. The position of the light source 40, the amount of emitted light from the light source 40, the direction of the optical axis of the condenser lens 40b, and the like are adjusted so that the charts 10 and 20 are irradiated with a sufficient amount of light. A single focus lens 50 is arranged after the charts 10 and 20. The single focus lens 50 is a lens having a focal length f of 16 mm and an aperture value F of 1.8. The aperture of the single focus lens 50 is used at full aperture (F1.8). The optical axis directions of the condenser lens 40b and the single focus lens 50 are the same. Then, the vibration tester 30 vibrates the charts 10 and 20 back and forth in the optical axis direction of the condenser lens 40b and the single focus lens 50. The charts 10 and 20 are fixed to the vibration tester 30 so as to overlap each other in the optical axis direction of the condenser lens 40b and the single focus lens 50.

A screen 60 is installed after the single focus lens 50. The light transmitted through the single focus lens 50 reaches the screen 60. The focus of the single focus lens 50 is set so as to alternately match one of the charts while the charts 10 and 20 are vibrating by the vibration tester 30. Therefore, when the charts 10 and 20 are vibrated by the vibration tester 30, an image in focus on one chart and an image in focus on the other chart appear alternately and repeatedly on the screen 60.

In the experimental device 1 configured as described above, the vibration tester 30 is vibrated in the optical axis direction of the condenser lens 40b and the single focus lens 50 at a frequency of about 60 Hz, and the charts 10 and 20 are projected on the screen 60. The image of was visually observed. As a result, when the vibration tester 30 is not operated and the focus of the single focus lens 50 is adjusted to one of the charts 10 and 20, the images of both charts 10 and 20 can be recognized on the screen 60 at the same time. There wasn't. However, when the charts 10 and 20 were vibrated by the vibration tester 30, the images of both charts 10 and 20 could be recognized on the screen 60 at the same time. In the optical system in which this experiment was performed, vibrating the chart position in the optical axis direction corresponds to changing the focal length of the optical element.

Next, the same experiment as above is performed using the experimental device 2 shown in FIG. The same components as those of the experimental device 1 are designated by the same reference numerals in the experimental device 2, and detailed description thereof will be omitted. In the experimental device 2, the liquid lens 70 is arranged between the charts 10 and 20 and the single focus lens 50. As the liquid lens 70, EL-8-16 manufactured by Optotune Co., Ltd. is used as an example. The focal length of the liquid lens 70 changes according to the magnitude of the applied current. The vibration tester 30 is not required in the experimental device 2.

In the experimental device 2, the charts 10 and 20 are fixed at a distance of 0.7 mm from each other in the optical axis direction of the condenser lens 40b and the single focus lens 50. In the experimental device 2, setting the distance between the charts 10 and 20 to 0.7 mm corresponds to a depth of focus of about 5D (Diopter).

In the experimental device 2, the light emitted from the light source 40 passes through the condenser lens 40b in the order of the charts 10, 20, the liquid lens 70, and the single focus lens 50, and reaches the screen 60. Regarding the current value of the current applied to the liquid lens 70, the grid figure attached to one of the charts 10 and 20 is projected on the screen 60 at 0 mA, and the grid figures attached to one of the charts 10 and 20 are projected on the screen 60 at 50 mA. The liquid lens 70 is configured so that the lattice figure attached to the other side is projected. Further, the current value applied to the liquid lens 70 is configured to change at a frequency of 35 Hz between 0 mA and 50 mA.

When the images of the grid figures of the charts 10 and 20 projected on the screen 60 were visually confirmed in the experimental apparatus 2 configured as described above, the images of the grid figures of both the charts 10 and 20 were recognized on the screen 60. I was able to. Further, the images of the grid figures of the charts 10 and 20 projected on the screen 60 are better recognized after the observation is continued for a certain period of time after the start of the application of the current to the liquid lens 70 than immediately after the start of the application of the current. I found that I could do it. Further, it was found that among the grid figures of the charts 10 and 20 projected on the screen 60, the image appeared more clearly toward the center of the chart, and the image deteriorated toward the periphery of the chart. It is considered that this is because the magnification of the image changes with the change of the focal length of the liquid lens 70.

(Example 1)
Next, as Example 1, the waveform when driving the vibration tester 30 or the liquid lens 70 in the above experimental device (hereinafter, also referred to as “changing the lens power” by combining the driving in the two cases). Will be described. FIG. 3 shows a general waveform when changing the lens power. As shown in FIG. 3, when the lens power is changed, it is often changed in a sinusoidal manner. In this case, the time for focusing on each focal position in the variable range of lens power is substantially uniform. Therefore, when this drive method is applied to the above-mentioned experimental apparatus, it takes a long time to focus on a place other than the chart 10 and the chart 20, and it is difficult to efficiently improve the imaging performance in the chart 10 and the chart 20. there were.

On the other hand, in this embodiment, as shown in FIG. 4, the lens power is changed in a rectangular shape between the lens power focused on the chart 10 and the lens power focused on the chart 20. According to this, during the period in which the lens power is changed, the time for focusing on the charts 10 and 20 is set to 1/2 of the total period, and the time for focusing on other places is set to substantially zero. be able to. According to this, the amount of light focused on the charts 10 and 20 can be increased as much as possible, and the imaging performance on the charts 10 and 20 can be selectively improved.

In the actual experiment, the liquid lens was tested using EL-8-16 manufactured by Optotune as an example. A driving current that changes in a rectangular shape at a frequency of 60 Hz was applied to the liquid lens 70 to change the focal position. At this time, the current values are rectangularly periodically cycled between chart 10 and chart 20.
Adjust so that it is in focus. In addition, the current value is changed in a square wave so that the position other than the position of the chart 10 and the position of the chart 20 can be passed in an instant, and the time for focusing on the position of the chart 10 and the position of the chart 20 is halved. And said. In this experiment, the chart 10 and the chart 20 could be seen, but even when another chart was provided between them, the other chart could not be seen well. From this, it is considered that the bifocal lens having the focus at the position of the chart 10 and the position of the chart 20 could be reproduced.

(Example 2)
Next, as the second embodiment, in FIG. 5, the lens power is changed so as to be evenly focused for a predetermined period at three points, a far point, a near point, and an intermediate point, and not to be focused at other places. An example will be described. In this example, the imaging performance is improved at three points, a far point, an intermediate point, and a near point, and it is possible to reproduce like a trifocal lens.

(Example 3)
Next, as Example 3, FIG. 6 shows an example in which the lens power is focused at two points, a far point and a near point, for a predetermined period of time, but not at other places. An example of focusing twice as long as the perigee will be described. As shown in FIG. 6, when the time when the apogee is in focus is doubled the time when the apogee is in focus, the apogee attracts twice as much light as the aphelion. Become. Here, it is known that the MTF at each focal point of the multifocal lens is proportional to the amount of light focused on each focal point. Therefore, in this embodiment, the MTF as shown in FIG. 7 is obtained at the far point and the near point, respectively, and the imaging performance becomes 2: 1. As described above, in this embodiment, by adjusting the time of focusing on each focal position, the MTF obtained at each focal point can be adjusted and the performance of various multifocal lenses can be reproduced. .. That is, the multifocal lens to be reproduced is not limited to two focal points, but may be three focal points, or may be a depth-expanded type called EDOF (Expanded Depth of focus or Field).

As in this embodiment, the example of changing the focusing time at the far point and the near point is not limited to the above waveform. The same effect can be obtained if the waveform is non-uniform vertically, such as a trapezoidal wave as shown in FIG. 8 or a waveform as shown in FIG.

The effect of the lens of the eye device in this embodiment is enhanced by wearing both eyes. When attached to both eyes, the changes in the lens power of one lens and the other lens may be temporally coincident or staggered. This is because, in the ophthalmic apparatus of this embodiment, the focus is changed in a cycle equal to or less than the time resolution at which the afterimage effect of a person appears, so that even if there is a time difference, there is no effect on the patient's vision. Because.

Further, the ophthalmic apparatus in this embodiment may have different states of change in lens power between the left and right eyes, as in the case of "monovision" prescribed in the ophthalmic industry. What is "monovision"? By inserting a single-focus intraocular lens into the dominant eye and a multifocal intraocular lens into the other eye, a wide depth of vision is obtained while maintaining the effect on the brain waves related to vision. The method. Like this "monovision", one eye (dominant eye) uses the lens of the eye device of the present invention, but does not change the lens power, and the other eye changes the lens power at high speed. May be good.

(Example 4)
A spectacle lens 100 as an example of the eye device according to the fourth embodiment of the present embodiment will be described with reference to FIG. The spectacle lens 100 is an optical element that changes the focal length of the optical system of the eyeball 160 by changing the radius of curvature or the refractive index with a change in voltage or current. The spectacle lens 100 corresponds to an example of a lens capable of electrically changing the focal length inserted into the optical system including the eyeball. A power supply unit 110 and an arbitrary waveform generator 120 are connected to the spectacle lens 100. The power supply unit 110 and the arbitrary waveform generator 120 correspond to an example of a power supply unit that supplies electric power that changes with a predetermined increase / decrease width to a lens at a time interval shorter than the time resolution of the eyeball. A function generator is exemplified as the arbitrary waveform generator 120. The power supply unit 110 and the arbitrary waveform generator 120 supply the spectacle lens 100 with a voltage or current that varies at a frequency of 30 Hz or higher, preferably 60 Hz or higher.

As the spectacle lens 100, a lens whose focal length, that is, refractive power changes at the above frequency, such as a so-called dynamorph lens or a liquid lens EL-8-16 manufactured by Optotune, can be adopted. The dynamorph lens is a varifocal lens in which the interface between liquids is used as a high-precision refracting surface and the focal length is changed by applying pressure to the liquid by a laminated piezo element. If the change in the refractive power of the spectacle lens 100 is set to 5D or more, it is considered that the accommodation power of the average eyeball of a so-called young person can be realized by the spectacle lens 100.

The power supply unit 110 and the arbitrary waveform generator 120 can supply a voltage or a current that changes the focal length (refractive power) of the spectacle lens 100 to the spectacle lens 100 30 times or more per second, preferably one second. Any device may be used as long as it can increase or decrease the voltage or current capable of changing the refractive power of the spectacle lens 100 by 5D or more 60 times or more over time.

When the above spectacle lens 100 is provided on the spectacle frame 130 made of an arbitrary material, shape, design, etc. and worn as the spectacle 140, the wearer of the spectacle 140 loses the adjusting power of the crystalline lens. However, it is possible to transmit an in-focus image to the brain over a range from distant to near.

Preferably, the spectacle lens 100 has an aperture diaphragm of φ3.0 mm or less. Alternatively, the spectacle lens 100 has an aperture diaphragm smaller than that of the human iris. In the eyeball optical system including the spectacle lens 100, the closer the position of the optical element whose focal length changes is to the position of the aperture that limits the light beam, the smaller the change in image size due to the change in focal length, which is better. It can be said that it can provide the wearer with a clear view. In the case of spectacles, since the optical region used differs depending on the change in the line of sight, a plurality of aperture diaphragms may be provided.

Further, preferably, the field diaphragm 150 is provided in the spectacles 140 configured as described above. In the eyeball optical system including the spectacle lens 100, the change in the image size (magnification) with the change in the focal length is larger in the off-axis peripheral portion than in the vicinity of the optical axis of the spectacle lens 100. Therefore, by providing the visual field diaphragm in the spectacles according to the present embodiment to limit the visual field of the wearer, the change in the magnification of the image is reduced and recognized by the wearer without providing a complicated optical region in the spectacles. It is possible to reduce the deterioration of the resulting image. In this embodiment, only the spectacle lens 100 may be held by the frame 130, and the other configuration may be separately worn, for example, on the wearer's body.

(Example 5)
The contact lens 200 as an example of the eye device according to the fifth embodiment of the present embodiment will be described with reference to FIG. The contact lens 200 is printed with an electric circuit 210 that changes the radius of curvature or the refractive index of the contact lens 200 according to a change in voltage or current. The contact lens 200 corresponds to an example of a lens capable of electrically changing the focal length inserted into the optical system including the eyeball. The focal length of the optical system of the eyeball 260 changes as the radius of curvature or the refractive index of the contact lens 200 changes. An arbitrary waveform generator 230 such as a power supply unit 220 and a function generator is electrically connected to the electric circuit 210. The power supply unit 220 and the arbitrary waveform generator 230 correspond to an example of a power supply unit that supplies electric power that changes with a predetermined increase / decrease width to a lens at a time interval shorter than the time resolution of the eyeball. The power supply unit 220 and the arbitrary waveform generator 230 provide the electrical circuit 210 with a voltage or current that varies at a frequency of 30 Hz or higher, preferably 60 Hz or higher, by wire or wirelessly.

The contact lens 200 is a contact lens capable of exchanging electrical information with the outside of the contact lens like a so-called smart contact lens, and the focal distance (refractive force) is determined based on the exchange of electrical information. Any contact lens that can be changed will do.

Also, for example, a zoomable contact lens can be used. The contact lens is equipped with a zoom function. Further, the contact lens has a region in which the zoom function is provided and a region in which the reflecting telescope is not provided.

The wearer of the contact lens also wears eyeglasses equipped with liquid crystal glass. The glasses are linked with the zoom function mounted on the contact lens. Specifically, when the power of the liquid crystal glass is turned on, the light incident on the liquid crystal glass is polarized and proceeds to the region where the reflecting telescope is provided. The image formed by the light traveling in the area where the zoom function is provided is magnified by, for example, the telephoto function. Further, when the power of the liquid crystal glass is turned off, the light incident on the liquid crystal glass is polarized and proceeds to the region where the zoom function is not provided. The image formed by the light traveling in the area where the zoom function is not provided is recognized by the wearer without being magnified by the zoom function. Therefore, by repeatedly turning the power supply of the liquid crystal glass on and off at a frequency of 30 Hz or higher, preferably 60 Hz or higher, the wearer of the contact lens and the liquid crystal glass can move from a distance to a near distance even if the adjusting power of the crystalline lens is deteriorated. It is possible to transmit an in-focus image to the brain over the range of. In this embodiment, the functions and roles of the contact lens and the eyeglasses may be reversed.

Further, in this embodiment, as in the case of the fourth embodiment, preferably, the contact lens 200 has an aperture diaphragm of φ3.0 mm or less. Alternatively, the contact lens 200 has an aperture diaphragm smaller than the human iris. Even in an eyeball optical system including a contact lens 200, the closer the position of the optical element whose focal length changes is to the position of the aperture that limits the light beam, the smaller the change in image size due to the change in focal length, which is better. It can be said that a good view can be provided to the wearer. Therefore, it is preferable that the aperture diameter of the contact lens 200 is set to be smaller than the iris of the wearer's eyeball.

Further, preferably, the contact lens 200 configured as described above may be provided with a field diaphragm. Even in the eyeball optical system including the contact lens 200, the change in the size (magnification) of the image due to the change in the focal length is larger in the off-axis peripheral portion than in the vicinity of the optical axis of the contact lens 200. Therefore, by providing a visual field diaphragm in the contact lens according to the present embodiment to limit the visual field of the wearer, it is possible to reduce the change in the magnification of the image and reduce the deterioration of the image perceived by the wearer. ..

(Example 6)
An air jet generator 300 as an example of the eye device according to the sixth embodiment of the present embodiment will be described with reference to FIG. The air jet generator 300 is a device such as a tonometer that temporarily deforms the shape of the cornea 360a of the eyeball 360 by the air pressure of the air jet. The air jet generator 300 includes an air jet unit 300a that injects air into the cornea of the eyeball at intervals shorter than the time resolution of the eyeball. In general, the tonometer calculates the intraocular pressure by applying an air jet that is instantaneously ejected to the cornea 360a to temporarily deform the cornea 360a and measuring the time until the cornea 360a returns to its original shape. It is known that the recovery time from deformation in the cornea of a general human eyeball is 10 to 20 ms. Therefore, it is considered that the cornea 360a repeats deformation and restoration by applying an air jet to the cornea 360a according to the restoration time from the deformation of the cornea 360a. Therefore, in this embodiment, the focal length of the optical system of the eyeball 360 is changed by deforming and restoring the cornea 360a by the air jet generator 300.

Here, the air jet generator may be separated from the cornea within the reach of the air jet, in addition to the configuration in which the air jet generator is arranged immediately in front of the eyeball like glasses. For example, when viewing a screen and a PC (Personal Computer) at a conference or the like, an air jet generator is placed on the desk in front of the user of the device, and the tracking result is tracked while tracking the movement of the eyeball using image processing or the like. Air may be injected from the air jet generator to the cornea based on the above. Further, the air jet generator may be held by hand so that the user can use the air jet generator when the adjustment function is required. Further, when it is assumed that the air jet generator is provided in a passenger car or the like and the air jet generator is used during operation, the air jet generator may be arranged near the steering wheel or the instrument.

It is known that the cornea has a predetermined curvature when the air jet is not applied, but when the air jet is applied, the cornea is deformed until the shape of the cornea becomes substantially flat. Further, it is generally known that the refractive power of the cornea is about 43D. From these facts, it is considered that the change in the shape of the corneal surface due to the air jet corresponds to the change of about 40D.

Therefore, in the present embodiment, the air jet generation device 300 sets the generation interval of the air jet in accordance with the above restoration time, and applies the air jet to the cornea 360a to repeatedly deform and restore the shape of the cornea 360a. It can be carried out. By repeating the deformation and restoration of the shape of the cornea 360a in this way, even if the adjustment force of the crystalline lens of the user of the air jet generator 300 is lost, the brain can obtain a focused image over a range from a distance to a near distance. Can be transmitted to.

When the radius of curvature of the front surface of the cornea is 7.7 mm, it is considered that the refractive power of the eyeball changes by about 5D when the radius of curvature increases to 8.5 mm. In this case, the position of the apex of the cornea is considered to move by about 20 μm toward the center of curvature of the cornea, but this amount of movement is considered to be smaller than the maximum amount of shape change due to the above air jet.

(Example 7)
The ultrasonic focusing device 400 as an example of the eye device according to the seventh embodiment of the present embodiment will be described with reference to FIG. The ultrasonic focusing device 400 is a device that generates ultrasonic waves as a non-contact acting force. The ultrasonic focusing device 400 generates a non-contact acting force of, for example, several tens of mN. The ultrasonic focusing device 400 has an ultrasonic generating unit 400a that generates ultrasonic waves focused on the front surface of the cornea of the eyeball at time intervals.

The susceptibility of the cornea to deformation affects the magnitude of intraocular pressure. It is known that the normal range of general intraocular pressure is 10 to 21 mmHg (corresponding to 1333 to 2800 Pa). Further, as an example, according to JIS (Japanese Industrial Standards) of a tonometer, the range of the cornea that is allowed to change its shape by an air jet is defined as a range within the diameter of the cornea of φ3.06 mm. Here, the force N given to the cornea by the air jet of the tonometer is calculated by the following equation (1) from the area of a circle having a diameter of 3.06 mm and the magnitude of the intraocular pressure.
Force applied to the cornea (N) = intraocular pressure (Pa) x area where the corneal shape changes (mm ² ) ... (1)

Using the area where the intraocular pressure and the corneal shape change, the force exerted by the air jet on the cornea can be estimated to be 9.8 to 21 mN from the equation (1). Therefore, it is considered that the shape of the cornea can be changed if the non-contact acting force of this magnitude can be applied to the cornea by the ultrasonic waves generated by the ultrasonic focusing device 400.

As described above, according to the ultrasonic focusing device 400 of the present embodiment, a force having the above magnitude can be applied to the cornea 460a of the eyeball 460 as a non-contact acting force. Further, since the ultrasonic focusing device 400 can control the generation of ultrasonic waves at a high frequency, the ultrasonic wave generation interval in the ultrasonic focusing device 400 is the same as that of the air jet generating device 300 of the sixth embodiment. Is set according to the above-mentioned restoration time, and ultrasonic waves are applied to the corneal 460a, so that the shape of the corneal 460a can be repeatedly deformed and restored. Therefore, in this embodiment, the focal length of the optical system of the eyeball 460 is changed by deforming and restoring the cornea 460a by the ultrasonic focusing device 400.

In this embodiment, the distance between the ultrasonic focusing device 400 and the cornea 460a can be adjusted by changing the focusing of the ultrasonic waves generated from the ultrasonic focusing device 400 in the cornea 460a. For example, an ultrasonic wave generating element is adopted as the ultrasonic wave focusing device 400, and the spectacles 420 in which the ultrasonic wave focusing device 400 is attached to the spectacle frame 410 are manufactured. Then, the ultrasonic focusing device 400 is adjusted so that the ultrasonic waves generated from the ultrasonic focusing device 400 are focused on the front surface of the cornea. The ultrasonic focusing device 400 is arranged at a position outside the field of view of the eyeball 460, and the ultrasonic waves are applied to the cornea 460a from a direction of a predetermined angle θ with respect to the optical axis AX of the eyeball 460. Therefore, even when the adjusting power of the crystalline lens of the wearer of the spectacles 420 thus produced is lost, a focused image can be transmitted to the brain over a range from a distance to a near distance.

(Example 8)
Next, the contact lens 500 as an example of the eye device according to the eighth embodiment of the present embodiment will be described with reference to FIG. The contact lens 500 is, for example, a soft contact lens, and it is preferable that a tear film 510 (or tear film) is formed between the cornea 560a of the eyeball 560 and the contact lens 500 when the contact lens 500 is worn.

In this embodiment, the wearer of the contact lens 500 also uses an eye device 520 that deforms the lens shape of the contact lens 500. The eye device 520 is, for example, the air jet generator 300 or the ultrasonic focusing device 400 of the above embodiment. Then, the eye device 520 is configured in the same manner as the air jet generator 300 or the ultrasonic focusing device 400 described above, and the surface of the contact lens 500 is deformed by the eye device 520 instead of the cornea 560a, whereby the eyeball 560 The focal length of the optical system changes. Therefore, even when the adjustment power of the crystalline lens of the wearer of the contact lens 500 and the eye device 520 configured in this way is lost, it is possible to transmit an in-focus image to the brain over a range from a distance to a near distance. can.

The above is the description of this embodiment. Phenomena peculiar to the human eye related in the present embodiment include afterimage effect, color constancy, chromatic adaptation, brightness constancy, light adaptation, and dark adaptation.

The afterimage effect is a phenomenon in which blinking of the human eyeball below the time resolution is perceived as continuous lighting. It is generally known that the time resolution of the human eyeball is about 50 Hz. For example, a general fluorescent lamp blinks at 50 Hz (blinks 100 times per second) or 60 Hz (blinks 120 times per second), so that the blinking of the fluorescent lamp is perceived by the human eye as continuous lighting. NS. Based on this, in the human eye, when the focal length changes at high speed, it is within the range of change of the focal length while the afterimage phenomenon of the object A occurs after the object A is focused at a certain distance. The object is in focus, and the object A is in focus again. As a result, the human eye perceives that the object A is in focus. Similarly, the human eye perceives any object within the range of change in focal length as in focus.

Next, color constancy refers to a phenomenon in which, for example, a person who has a color sense that tomatoes are red recognizes tomatoes as red even when they see the tomatoes through a color filter. For example, when observing tomatoes by displaying them on a monitor, when a person who has a color sense that tomatoes are red observes tomatoes that have passed through a color filter on the monitor, they are classified as gray or blue on the monitor. Colored tomatoes may be recognized as red. Based on this, in the above embodiment, the focal length changes at a high speed, but even if the colors of the image that are momentarily out of focus are mixed when the focal length changes, the human color perception is felt. Therefore, the mixed colors are perceived as the colors of the image when they are in focus. In addition, considering that the human eye perceives an in-focus image more strongly than an out-of-focus image, the eye device of the present embodiment provides a field of view that is unlikely to give a sense of discomfort. It is believed that it can be provided to the human eye.

Next, chromatic adaptation refers to the function of adjusting the sensitivity of the cone according to the surrounding spectral distribution to keep the color appearance constant. If you look at the same grayscale image immediately after looking at an image with a certain color for several tens of seconds, it is recognized as a colored image. It is also a phenomenon in which the color disappears from the image and is perceived when the image to which the color including the color is applied is viewed immediately after the color is continuously viewed for several tens of seconds. Based on this, by using the ophthalmic lens of the present embodiment, in addition to the above-mentioned effect of color constancy, the human eye is provided with a field of view that is unlikely to give a sense of discomfort when the focal length changes at high speed. Can be provided.

For example, even if the color of an object is recognized as a color different from the original color due to the mixture of images that are out of focus due to changes in the focal length, due to the characteristic of color constancy, humans The eye tends to perceive that the color of the object remains the original color rather than perceived as having changed. In addition, even if the state of recognizing a different color continues, chromatic adaptation works and the color is gradually recognized as the original color.

Next, brightness constancy refers to a phenomenon in which the human eye perceives the brightness of light based on the reflectance of light, not on the basis of absolute light intensity. It is known that the brightness of light perceived by the human eye depends on the relative amount of change from the periphery of the object rather than the absolute amount of optics. That is, even if the colors have the same brightness, if the surrounding color is dark, it is perceived as a brighter color, and if the surrounding color is bright, it is perceived as a darker color. Based on this, when the eye device of the present embodiment is used, the contrast in the entire field of view may decrease due to the momentarily out-of-focus image, but the brightness of the human eye is constant. It is considered that the contrast is improved by the sex. For example, when the focal length is changing at high speed, the in-focus image and the out-of-focus image are perceived as a mixture, and the contrast of the image in the field of view is reduced, resulting in black and white. Even when they approach gray, it is considered that the contrast decreases at all focal lengths within the range of change of focal lengths. As a result, the decrease in contrast is less likely to be recognized by the human eye due to the homeostasis of brightness.

In addition, since the human eye recognizes the in-focus image more strongly, there is a difference in brightness between the object that the human eye is paying attention to and its surroundings in the same color. Recognize the boundaries of objects based on relative differences. For example, in a vision test using a Randolt ring, the human eye corrects the decrease in contrast while continuing to look at the Randolt ring, even if the image of the Randolt ring is slightly out of focus. Can perceive the breaks in. In this way, the human eye can correct the decrease in contrast in the visual field. Therefore, when the eye lens of the above embodiment is used, the contrast is improved even if the decrease in contrast occurs in the entire visual field, and the visual field is improved. The effect of increasing the depth of focus can be expected.

Here, the effect of brightness homeostasis on depth increase will be described in detail. When the focal length is changed at high speed, the human eye simultaneously recognizes an in-focus image and an out-of-focus image. At this time, since the out-of-focus image is superimposed on the in-focus image, the human eye perceives a dark image with temporarily reduced contrast. However, in the depth of focus range increased with the change of the focal length, the contrast decrease due to the out-of-focus image causes a uniform decrease in contrast with respect to the field of view, that is, a uniform decrease in brightness over the entire field of view. It is considered to be equivalent to the state in which it was used. On the other hand, since the human eye can easily recognize an image in which the object is in focus, the image in focus is perceived as relatively stronger and brighter than the image in focus. In this way, the human eye perceives the image of the in-focus object as relatively stronger and brighter than the out-of-focus image, so that the information other than the object is recognized as peripheral information. When the homeostasis of brightness works in this state, the human eye compares the darkness of the surrounding information with the relative brightness of the object, and the object is more easily recognized. That is, in the human eye, the decrease in contrast due to the out-of-focus image is improved, so that the effect of increasing the depth caused by the change in the focal length can be expected.

Next, light adaptation is a phenomenon in which, for example, when moving from a bright place to a dark place, nothing can be seen at first, but the eyes gradually get used to it and gradually become visible. Further, dark adaptation is a phenomenon in which the eyes become accustomed and gradually become visible when moving from a dark place to a bright place. It is known that the human eye exerts light adaptation in about 1 minute and dark adaptation in about 1 hour. From this, when the eye device of the above embodiment is used, even if the entire field of view is darkened by an image that is momentarily out of focus, these adaptations are exhibited to darken the entire field of view. Is expected to be improved.

The ophthalmic lens according to the present embodiment is configured in consideration of the characteristics of each phenomenon of the human eye described above. No. Further, in the prior art, the decrease in contrast is only improved by image processing using an image sensor such as a camera or a monitor. When a camera or the like is a component of an eye device, the generated image is affected by the shutter speed and pixel sensitivity. In addition, the pixels integrate the intensity of light and convert it into electric charges. Since the contrast difference between images is created by superimposing images, it may be recognized that the depth becomes deeper as a result of the high contrast part remaining in the human brain, but as visual information processing of the retina and brain. It is different from the afterimage phenomenon of. In the afterimage phenomenon of the retina and visual information processing in the present invention, the brain continuously recognizes an image in focus directly without going through an image generator such as a camera, thereby utilizing phenomena such as adaptation and homeostasis. It can provide a better view.

The configuration provided in the above-mentioned ophthalmic device is not limited to the above-described embodiment, and various changes can be made as long as the same as the technical idea of the present invention is not lost. Three examples of modifications of the above embodiment are shown below. It should be noted that the configuration described in the above embodiment and the configuration described in the modification described below can be freely combined. Further, in the following description, the same components as those in the above-described embodiment will be designated by the same reference numerals, and detailed description thereof will be omitted.

(Modification example 1)
The power supply unit 600 according to the first modification of the present embodiment will be described with reference to FIG. The power supply unit 600 is, for example, a solar cell film having light transmission using an organic thin film. The power supply unit 600 is mounted inside the ophthalmic lens or contact lens described in the above embodiment. For example, instead of the power supply unit 110 connected to the spectacle lens 100 as shown in FIG. 15, the power supply unit 600 according to this modification can be provided in the spectacle lens 100 to form the spectacle 610. ..

The energy of sunlight is about 1 kW / m ² , and the conversion efficiency of a general solar cell is about 10%.
Is known to be. That is, the power generation of the solar cell can be estimated to be 0.1 mW per ^{1 mm 2.} In the liquid lens EL-8-16 manufactured by Optotune, which is an example of the spectacle lens 100 of the above embodiment, in order to achieve a change in refractive power of about 5D, a power consumption of about 50 mA at 1.8 V, that is, 90 mW is required. It becomes.

When the power supply unit 600 is provided in the spectacle lens 100, if the area of the power supply unit 600 is 1000 mm ² (for example, 5 cm × 2 cm), the power generation of the power supply unit 600 can be estimated to be 0.1 mW × 1000 = 100 mW. .. That is, it can be said that the power supply unit 600 can generate electric power exceeding the power consumption required when the liquid lens EL-8-16 manufactured by Optotune is used as an example of the spectacle lens 100.

(Modification 2)
Next, the eye lens 700 according to the second modification of the present embodiment will be described with reference to FIG. The ophthalmic lens 700 is formed to include a speaker film having light transmission. The speaker film is formed by sandwiching a light-transmitting thin film made of a piezoelectric substance between light-transmitting films having good vibration transmission characteristics. A thin film made of a piezoelectric substance functions as a diaphragm when electric power is supplied.

The speaker film vibrates depending on the frequency of sound. Further, it is known that the frequency of sound that can be heard by humans is 20 Hz to 20 kHz, and electric power is supplied to the speaker film so as to vibrate in this frequency range. Therefore, vibration of 60 Hz or higher can be realized by using the speaker film.

That is, for example, as shown in FIG. 16, by using the eye lens 700 instead of the contact lens 200 of the above embodiment, even if the adjusting power of the crystalline lens of the wearer of the eye lens 700 is lost, it is far away. It is possible to transmit an in-focus image to the brain over a range from to near.

(Modification example 3)
Next, the intraocular lens 800 according to the third modification of the present embodiment will be described with reference to FIG. In the fifth embodiment, the contact lens 200 is provided with a field diaphragm to limit the field of view of the wearer, thereby reducing the change in the magnification of the image and reducing the deterioration of the image perceived by the wearer. I explained what you can do. Considering that the iris of the eyeball functions as an aperture diaphragm and a field diaphragm, an intraocular lens 800 on which an electric circuit 210 is printed is configured so that the focal distance changes, and an intraocular lens is further formed, similar to the contact lens 200. By inserting the 800 immediately after the iris 860a of the eyeball 860, the wearer of the intraocular lens 800 can use the iris 860a as an aperture diaphragm and a field diaphragm to obtain a focused image over a distant to near range. Can be transmitted to. The configuration of the intraocular lens that changes the focal length may be a configuration in which the radius of curvature of the lens changes due to a change in current or voltage like a liquid lens, in addition to the configuration in which the electric circuit 210 is printed, and there are a plurality of lenses. It may be composed of optical elements and the distance between the optical elements may be changed, or the refractive index of the optical element material may be changed.

In the above-mentioned examples and modifications, an example in which the present invention was used for recovery of visual function of a patient was described. However, the object of application of the present invention is not limited to the actual recovery of visual function of a patient. The present invention may be applied to an optometric lens that confirms the appearance of the multifocal lens prior to the operation of inserting the multifocal intraocular lens in place of the crystalline lens. In that case, the patient changes the lens power of the optometry lens according to the drive waveforms shown in FIGS. You just have to decide the specifications that match the image of.

According to this, it is possible to surgically insert a multifocal intraocular lens having specifications that the patient is satisfied with. In addition, since the patient can experience the appearance after the operation before the operation, it is possible to avoid troubles caused by the difference between the image of the patient before the operation and the actual appearance after the operation.

100 Eyeglass lens 160, 260 Eyeball 200 Contact lens 210 Electric circuit 220, 600 Power supply unit 230 Arbitrary waveform generator 300 Air jet generator 400 Ultrasonic focusing device 500 Contact lens 700 Eye lens 800 Intraocular lens

Claims (12)

An eye device having an element that changes the focal length of an optical system including an eyeball at a time interval shorter than the time resolution of the eyeball.
The element changes the focal length of the optical system including the eyeball so as to be uneven in time in the variable range of the focal length .
The element determines the time during which the focal length of the optical system including the eyeball becomes a predetermined focal length in the variable range of the focal length according to the MTF required at the predetermined focal length.
In the variable range of the focal length, the element changes the focal length of the optical system including the eyeball so as to be stopped for a predetermined time at each of the plurality of focal lengths.
The predetermined time is, the ophthalmic device, wherein Rukoto determined based on the ratio of the MTF required in the optical system including the eye in each of the plurality of focal lengths. In the variable range of the focal length, the element has a time when the focal length of the optical system including the eyeball becomes a predetermined first focal length, and a second focal length whose focal length is different from the first focal length. The ophthalmic apparatus according to claim 1, wherein the focal length of the optical system including the eyeball is changed so as to be longer than the time required. The first or second claim, wherein the change waveform when the element changes the focal length of the optical system including the eyeball includes any one of a square wave, a triangular wave, a sine wave, and a trapezoidal wave. Eye device. The eye device according to any one of claims 1 to 3 , wherein the eye device includes a contact lens that comes into contact with the eyeball and forms a part of an optical system including the eyeball. The eye device according to any one of claims 1 to 3 , wherein the eye device includes eyeglasses that form a part of an optical system including the eye ball in a state of being separated from the eye ball. The eye device according to any one of claims 1 to 3 , wherein the eye device includes an optometry lens worn by a patient before an operation of inserting a multifocal intraocular lens. The eye device according to any one of claims 1 to 3 , wherein the eye device includes a vibrating film that constitutes a part of an optical system including the eyeball. The ophthalmic apparatus according to any one of claims 1 to 7 , wherein the element changes the focal length by any of electromagnetic force, voltage, current, ultrasonic waves, and air pressure. The eye device according to any one of claims 1 to 8 , wherein the element changes only the focal length of an optical system including an eyeball of one eye. The eye device according to any one of claims 1 to 8 , wherein the element changes the focal length of an optical system including the eyeballs of both eyes. The eye device according to claim 10 , wherein the state of change in the focal length in the eyeballs of both eyes is the same. The eye device according to claim 10 , wherein the state of change in the focal length in the eyeballs of both eyes is different.

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