WO2012157623A1

WO2012157623A1 - Intraocular lens

Info

Publication number: WO2012157623A1
Application number: PCT/JP2012/062354
Authority: WO
Inventors: 哲也江口; 安弘刑部; 和典宮田
Original assignee: Hoya株式会社
Priority date: 2011-05-17
Filing date: 2012-05-15
Publication date: 2012-11-22
Also published as: JP2012239530A

Abstract

An intraocular lens has an optical unit with a predetermined refractive power and a support part that supports the optical part in the lenticular capsule, wherein the support part has a sensor that measures the pressure in the vitreous body via the posterior capsule in the lenticular capsule, and the optical unit has an antenna section that transmits the pressure that was measured by the sensor to the outside.

Description

Intraocular lens

The present invention relates to an intraocular lens, and more particularly, to an intraocular lens mounted in a lens capsule.

白 Cataract is known as a disease related to the human eye. This “cataract” is a disease that causes a decrease in visual acuity and the like due to white turbidity of the lens that performs the lens function inside the eyeball.

”Cataract surgery + intraocular lens implantation is performed to restore the visual acuity of patients who have developed this cataract. The above-described operation is an operation for removing a white cloudy lens and inserting an artificial intraocular lens (IOL: IntraOcular Lens) therein.

An intraocular lens implanted in the eye by intraocular lens transplantation is constituted by an optical part having a predetermined refractive power instead of a crystalline lens and a support part that supports the optical part. This type of intraocular lens is most preferably housed in the capsular bag that remains after the lens is removed. As a result, normal visual acuity can be ensured by an intraocular lens instead of a white cloudy crystalline lens.

However, glaucoma exists as a human eye disease that causes vision loss. This glaucoma often occurs with cataracts. Moreover, even if only cataract has developed, the possibility that glaucoma will develop later cannot be denied.

This “glaucoma” is a progressive disease that causes visual field abnormalities (specifically visual field defects). If this glaucoma develops and the visual field is lost, it is difficult to recover the visual field once lost, which can cause blindness.

Here, the glaucoma and the matter considered as the onset factor (progression factor) will be briefly described.
FIG. 5 is an explanatory diagram of an outline of glaucoma.
As shown in FIG. 5A, the eyeball 1 is always kept round. This is because the eyeball 1 is filled with a gel-like substance called vitreous and water-soluble aqueous humor. The eyeball 1 is kept in shape because there is an intraocular pressure determined by the balance of aqueous humor produced from the ciliary epithelium 10 and its outflow from the corner and the episcleral vein pressure. is there.

As shown in FIG. 5 (b), the aqueous humor is secreted from the site of the ciliary epithelium 10, passes between the lens capsule 8 and the iris 6, reaches the anterior chamber, and passes through the trabecular belt 18a to the Schlemm's canal. It circulates through a fixed route that is discharged from 18b and flows to a blood vessel outside the eye. In addition, the place of the outflow path of the aqueous humor including the trabecular meshwork 18 a is referred to as a corner 18.

As shown in FIG. 5 (c), glaucoma is a disease in which the intraocular pressure is increased and the optic nerve 15 is damaged, resulting in characteristic optic disc disorders and abnormal visual functions such as visual field abnormalities. In other words, measuring intraocular pressure as accurately as possible may prevent the progression of glaucoma.

Various devices for measuring this intraocular pressure are known. Hereinafter, for convenience of explanation, common items such as human eyeballs are denoted by the same reference numerals in Patent Documents 1 to 5 as those described in the drawings of the present application (particularly FIGS. 1 and 5).

For example, Patent Document 1 discloses a method in which the tip of a probe pen is brought into contact with the eyeball 1 and the intraocular pressure is measured through a vibration propagation liquid.

Further, in Patent Document 2, air is sprayed onto the cornea 2 of the eye to be examined, the deformation of the cornea 2 is optically detected, and the intraocular pressure of the eye to be examined is determined based on the air pressure when the applanation of the cornea 2 is detected. A method of measuring is disclosed.

Patent Document 3 discloses a method for measuring intraocular pressure based on a state of a pulse wave incident on the eyeball 1 of the eye to be examined and a state of a reflected wave in which the incident pulse wave is reflected from the eyeball 1. It is disclosed.

Also, Patent Document 4 discloses an antenna in which an intraocular lens is disposed inside an annular support member having a coil provided on the outer periphery as an antenna. Note that an electronic module is provided on a part of the annular support member at a position where it comes into contact with the intraocular lens. This electronic module is provided with a sensor, and in the crystalline lens capsule that receives the intraocular lens, on the outer side of the eye (the direction in which the cornea 2 is seen from the crystalline lens capsule 8) with the ciliary zonule (chin zonule) 9 in between. The part (substantially elliptical front half) is the anterior capsule 8a, and the part inside the eye (the direction in which the optic nerve 15 is seen when viewed from the lens capsule 8) is sandwiched between the chin zonules 9 (substantially elliptical rear half). 8b, this sensor is configured to measure the pressure on the anterior capsule 8a. In order to show this, in FIGS. 1 and 2 (plan view) of Patent Document 4, the sensor faces the anterior capsule 8a side, and in FIG. 4 (cross-sectional view) of Patent Document 4, the sensor is on the anterior capsule 8a side. It is exposed in the direction.

Further, Patent Document 5 discloses an intraocular lens having a antenna and a sensor used as an antenna (for example, FIGS. 99A to 99C of Patent Document 5). As an application of this sensor, the measurement of intraocular pressure is disclosed in paragraph [0127] of the same document, for example. In addition, it is described in paragraph [0865] of the document that a sensor is attached to one of antennas used as an antenna.

JP 2004-267299 A JP 2007-275315 A JP 2010-172464 A Japanese Patent No. 4251387 JP 2011-005261 A

In the intraocular pressure measuring devices described in

Patent Documents

1 and 2, an operation is performed in which the amount of displacement of the cornea 2 of the eye to be examined is measured and the intraocular pressure is calculated from the amount of displacement. On the other hand, there are individual differences in the thickness and elasticity of the cornea 2 of the subject. Therefore, when a conventional intraocular pressure measuring device is used, the amount of displacement of the cornea 2 is measured low due to the characteristics of the cornea 2 of the subject despite the fact that symptoms of glaucoma have started to appear and the intraocular pressure has increased. Therefore, it cannot be denied that there is a possibility of being judged not to have glaucoma.

Therefore, it is necessary to provide an absolute value standard for determining the possibility of progression of glaucoma for what is obtained as an absolute value parameter (for example, intraocular pressure) for any subject.

Furthermore, in the intraocular pressure measuring devices described in Patent Documents 1 to 3, the intraocular pressure of the subject is determined only after the subject wears the measuring device. In other words, whether or not the intraocular pressure of the subject is normal or abnormal can only be determined by measuring the intraocular pressure with an intraocular pressure measuring device. That is, when intraocular pressure is measured, there is a possibility that glaucoma has already developed and visual field loss has already occurred. Therefore, from the viewpoint of preventing the progression of glaucoma, it is highly desirable to measure the intraocular pressure of the subject in real time.

In addition, Patent Documents 4 to 5 certainly describe that a sensor is provided in an intraocular lens. However, as described above, the onset mechanism of glaucoma causes an increase in intraocular pressure due to an increase in the amount of aqueous humor that constitutes the vitreous body 11 in the eye, and causes compression of the optic nerve 15 to cause visual field loss. It is said that. As a result, in order to prevent the visual field defect from proceeding, it is highly desirable to measure the pressure of the vitreous body 11 that directly presses the optic nerve 15 rather than the pressure inside the lens capsule 8. Note that the pressure of the vitreous body 11 when the optic nerve 15 is compressed by the vitreous body 11 is also referred to as “pressure in the vitreous body 11”.

However, a method for measuring the pressure inside the vitreous body 11 instead of the inside of the lens capsule 8 in real time is not yet known. Furthermore, in order to prevent the progression of glaucoma, the literature that motivates the measurement of the pressure in the vitreous body 11 instead of the pressure in the capsular bag 8 is not yet known.

Therefore, the main object of the present invention is to provide an intraocular lens that suppresses the progression risk of glaucoma by measuring in real time a pressure that is the same as or very close to the intravitreal pressure.

In order to solve the above-mentioned problem, the present inventor examined “how to measure the pressure in the vitreous body 11 by the intraocular lens disposed inside the lens capsule 8”. In addition, “how to measure the value in accordance with the pressure in the vitreous body 11 in real time” was also examined.

At the time of this review, the above patent document was reviewed. In the patent literature, 1-2 were reexamined.

Whether the contact-type intraocular pressure measurement device as in Patent Document 1 or the non-contact-type intraocular pressure measurement device as in Patent Document 2, the amount of displacement of the cornea 2 of the eye to be examined is used as a basis for measuring intraocular pressure. It was. Assuming that a sensor for measuring the amount of displacement of the cornea 2 of the eye to be examined is provided by an intraocular lens as in the above-mentioned patent document, an optical unit (in particular, a person wearing the intraocular lens of the intraocular lens). It would be preferable for those skilled in the art to provide a sensor and a member covering the periphery thereof in a portion that does not enter the field of view. This is because in order to measure the amount of displacement of the cornea 2, the actual amount of displacement can be measured more accurately if the sensor unit is provided near the portion where the amount of displacement is the largest.
Hereinafter, the person wearing the intraocular lens is also simply referred to as “wearer”. Further, a member covering the sensor and its surroundings is also simply referred to as a “sensor unit”.

Under such circumstances, the present inventor reexamined the cause of glaucoma away from the intraocular pressure measurement method as described in

Patent Documents

1 and 2. At that time, glaucoma focused on the fact that the pressure in the vitreous body 11 that compresses the optic nerve 15 is the main factor of glaucoma rather than the pressure in the entire eye. Based on this focus, the inventor has conducted extensive research and found that the pressure in the vitreous body 11 can be transmitted to the intraocular lens very faithfully through the posterior capsule 8b of the lens capsule 8. Obtained.

However, the present inventor has realized that various inconveniences may occur when the sensor unit is provided in the optical unit as in the past in order to realize this knowledge. That is, in the past, in order to measure the displacement amount of the cornea 2, a sensor unit was provided in the vicinity of the portion with the largest displacement amount (that is, the optical unit). It is necessary to always or almost always contact with the sac 8b. Otherwise, the pressure in the vitreous body 11 cannot be accurately transmitted to the sensor unit in real time.

In order to realize this, it is preferable that the intraocular lens does not always move so much in the lens capsule 8 so as not to release the contact state of the lens capsule 8 with the posterior capsule 8b.
However, when the optical part in the intraocular lens is arranged in the capsular bag 8, it is located at a substantially central portion in the capsular bag 8. Further, not only when performing intraocular pressure measurement as in

Patent Documents

1 and 2, but also by performing an operation such as a wearer of the intraocular lens rubbing the eye, an impact is applied to the intraocular lens, and the lens capsule 8 The intraocular lens is displaced in the optical axis direction of the optical unit. Then, the contact state between the posterior capsule 8b and the intraocular lens in the lens capsule 8 is released. In particular, since the optical part of the intraocular lens is suspended and supported by the support part in the crystalline lens capsule 8, the amount of displacement is particularly large, and the contact state with the posterior capsule 8b is easily released. As a result, it becomes difficult to measure the pressure in the vitreous body 11 in real time.

In order to solve the above-mentioned problem obtained by the present inventor, the present inventor does not provide a sensor unit in the optical unit, but arranges it in the lens capsule 8 as shown in FIG. A configuration has been conceived in which the sensor unit 40 is provided on the support unit 22 having a relatively small displacement. And the structure which transmits the numerical value of the pressure in the vitreous body 11 from the sensor part 40 in the support part 22 to the antenna part 30 in the optical part 21, and also transmitted the numerical value of the pressure to the exterior was devised.

That is, in order to measure the intraocular pressure by displacing the cornea 2, the sensor unit 40 is not provided in the optical unit 21 which is a large displacement amount, but on the contrary, the support which is a relatively small displacement portion is supported. The sensor part 40 was provided in the part 22, and the knowledge that the pressure in the vitreous body 11 transmitted from the back capsule 8b was measured was acquired.

Aspects of the present invention based on the above findings are as follows.
The first aspect of the present invention is:
An intraocular lens comprising: an optical part having a predetermined refractive power; and a support part that supports the optical part in the lens capsule.
The support part is provided with a sensor part for measuring the pressure in the vitreous through the posterior capsule in the crystalline lens capsule,
In the intraocular lens, the optical unit is provided with an antenna unit that transmits the pressure measured by the sensor unit to the outside.
According to a second aspect of the present invention, in the invention according to the first aspect,
The sensor unit is provided in a portion of the support unit near a boundary between the optical unit and the support unit.
According to a third aspect of the present invention, in the invention according to the first or second aspect,
When the intraocular lens is inserted into the crystalline lens capsule, the sensor section is provided on the support section so that the sensor section is positioned in the vicinity of the posterior capsule.
According to a fourth aspect of the present invention, in the invention according to any one of the first to third aspects,
The optical part is formed of a soft material,
In the support part, at least a part of the vicinity of the boundary between the optical part and the support part is formed of a hard material as compared with the soft material,
The sensor unit is provided in at least a part of the above.

According to the present invention, the risk of progression of glaucoma can be suppressed by measuring in real time a pressure that is the same as or very close to the intravitreal pressure.

It is explanatory drawing which shows the planar cross-section of an eyeball. 1A and 1B are explanatory views showing a configuration example of an intraocular lens according to an embodiment of the present invention, in which FIG. 3A is a plan view, FIG. (D) is a cross-sectional view taken along the line BB 'when the boundary portion between the optical part and the support part in the intraocular lens is enlarged. The A-A ′ line is also a folding line of the intraocular lens. It is explanatory drawing which shows the usage method of the intraocular lens which concerns on one Embodiment of this invention, (a) is explanatory drawing which shows the place where an intraocular lens is inserted in a crystalline lens capsule, (b) is explanatory drawing which shows after insertion Fig. 3 (c) is an explanatory view showing how the capsular bag conforms to the intraocular lens after insertion of the intraocular lens. Fig. 3 (d) shows the pressure inside the vitreous via the posterior capsule (and the member surrounding the sensor). It is explanatory drawing which shows a mode that it transmits to a sensor part. It is explanatory drawing of the manufacturing method of the intraocular lens which concerns on one Embodiment of this invention. It is explanatory drawing which shows the outline | summary of glaucoma.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
In the present embodiment, description will be given in the following order.
1. Structure of eyeball A) Overall structure of eyeball B) Lens C) Lens capsule Intraocular lens A) Overall structure of intraocular lens B) Optical part (including antenna part)
C) Support part (including sensor part)
3. 3. Manufacturing method of intraocular lens 4. Use of intraocular lens Effects of the embodiment 6. Modified example

<1. Eyeball Structure>
Prior to the description of the intraocular lens according to the present invention, the structure of the eyeball in which the intraocular lens is used will be described.

A) Overall Structure of Eyeball FIG. 1 is a diagram illustrating a planar cross-sectional structure of an eyeball.
As shown in the figure, the eyeball 1 has a spherical shape as a whole, and is covered and protected by the sclera 3 except for the front cornea 2. The surface of the sclera 3 around the cornea 2 is covered with a conjunctiva 4. The cornea 2 functions not only as an eyeball protection function but also as a lens that refracts incoming light. On the inner side (back side) of the cornea 2 is an anterior chamber 5 filled with aqueous humor, and a pupil 7 is located in the center of the iris 6 facing the anterior chamber 5.

The iris 6 functions to adjust the amount of light incident on the inside of the eyeball 1 by adjusting the size of the pupil 7 (the size of the opening). The front surface of the lens capsule 8 faces the pupil 7. A ciliary epithelium 10 is connected to the lens capsule 8 via a ciliary zonule (chin zonule) 9. The ciliary epithelium 10 is a muscular tissue that focuses by controlling the thickness of the lens capsule 8.

There is a vitreous body 11 behind the capsular bag 8. The vitreous body 11 occupies most of the inside of the eyeball 1. The vitreous body 11 is a jelly-like colorless and transparent tissue, and maintains the shape and elasticity of the eyeball 1. Further, the vitreous body 11 functions to send the light refracted by the lens capsule 8 to the retina 13. The retina 13 is a membrane tissue located on the innermost side in the eyeball 1. In the retina 13, there are photoreceptor cells that sense light incident into the eyeball 1 through the pupil 7 and identify its intensity, color, shape, and the like.

There is a choroid 14 outside the retina 13. The choroid 14 is a membrane tissue located inside the sclera 3 (that is, between the sclera 3 and the retina 13). The choroid 14 is rich in blood vessels, and also serves as a blood flow path to each tissue of the eyeball 1 to give nutrition to the eyeball 1. Furthermore, an optic nerve 15 is connected to the back side (back side) of the eyeball 1. The optic nerve 15 is a nerve that transmits light stimulation received by the retina 13 to the brain. A blind spot 16 is present at a portion where the optic nerve 15 is connected. The blind spot 16 is located 4 to 5 mm away from the fovea 17.

B) Lens The lens is colorless and transparent and has a convex lens shape via the lens capsule 8, and a muscle called the ciliary epithelium 10 is connected and supported by the chin zonule 9. The lens becomes thicker when the ciliary epithelium 10 contracts and the chin strip 9 relaxes when looking closer. On the other hand, when looking at the distance, the ciliary epithelium 10 relaxes and the chin band 9 is pulled, so that it becomes thin. In this way, the crystalline lens is focused on the perspective.

C) Lens capsule The surface of the lens is wrapped with a thin film called the lens capsule 8. The lens capsule 8 is a film-like structure rich in elasticity, and maintains its properties under constant pressure. In the lens capsule 8, the outer portion of the eye across the ciliary zonule (chin zonule) 9 is referred to as the “anterior capsule”, and the eye is viewed from the chin zonule 9. The inner part is called the “posterior capsule”.

<2. Intraocular lens>
Next, the intraocular lens will be described. The intraocular lens in the present embodiment is assumed to be attached when the lens is extracted by an eye cataract surgery.

A) Overall Structure of Intraocular Lens FIG. 2 is an explanatory diagram showing a configuration example of the intraocular lens 20.
As shown in FIG. 2, the intraocular lens 20 includes an optical part 21 having a substantially circular shape in plan view, two arm-like and wire-like support parts 22 extending from the outer peripheral part of the optical part 21, and It is composed of The optical unit 21 and the support unit 22 can be formed of different materials, but in the present embodiment, both are formed integrally.

In the present embodiment, a case where a soft material (soft acrylic) is used for the optical part 21 and a soft material (soft acrylic) and a hard material (PMMA (polymethyl methacrylate)) are used for the support part 22 will be described. In addition, PMMA is used for the portion near the boundary between the optical unit 21 and the support unit 22 and the outermost portion (hereinafter also referred to as the tip 22c) as viewed from the center of the optical unit 21 in the support unit 22. Soft acrylic is used for the support 22 other than the above.

Further, in the present embodiment, a step portion 21 a is provided at the boundary portion between the optical unit 21 and the support unit 22. This stepped portion 21 a makes it easy for the optical portion 21 to be in close contact with the posterior capsule 8 b of the crystalline lens capsule 8 reliably. Therefore, it becomes possible to suppress the migration of the lens epithelial cells to the rear surface 20b side of the intraocular lens 20, and it is possible to suppress the risk of subsequent cataract progression caused by the lens epithelial cells.

In addition, it is preferable that the level | step difference of the level | step-difference part 21a is a level | step difference of the grade which the sensor part 40 of the support part 22 and the back capsule 8b can contact always or substantially always, and will give it a level | step difference of about 0.05 mm as an example. Is mentioned.

B) Optical part (including antenna part)
The optical unit 21 is located at the approximate center of the entire intraocular lens 20, and the shape thereof is a circular or elliptical part in plan view. The optical unit 21 has a predetermined refractive power. This refractive power secures the refractive power of the lens removed to cope with cataract. That is, when the intraocular lens 20 is inserted into the crystalline lens capsule 8 and light from outside the eye passes through the optical unit 21, the wearer of the intraocular lens 20 can obtain the refractive power before removing the crystalline lens. . FIG. 2 shows a case where both the front surface 20a and the rear surface 20b of the intraocular lens 20 (particularly the optical unit 21) have a convex shape.

The antenna unit 30 is formed on the outer periphery of the optical unit 21. The sensor unit 40 (described later) in the support unit 22 is operable by the power received by the antenna unit 30.

The antenna unit 30 is configured by covering a plurality of proximity coil windings 31 with members constituting the optical unit 21. The coil winding 31 is arranged in an annular shape so as to circulate around the optical axis of the optical unit 21, and a plurality of coil windings 31 are arranged close to each other. The plurality of coil windings 31 are embedded in the optical unit 21.

The coil winding 31 exists in a ring shape in a plane orthogonal to the optical axis. By doing so, when the intraocular lens 20 (and thus the optical unit 21) is folded, damage to the antenna unit 30 can be suppressed and high transmission / reception characteristics can be maintained, and the intraocular lens 20 can be folded relatively easily. Can do.

The coil winding 31 in the antenna unit 30 is arranged on the outer periphery of the optical unit 21, so that a certain length in the coil winding 31 can be ensured even if the intraocular lens 20 is downsized. As a result, power can be supplied from the outside using electromagnetic induction to the electronic module 32 (described later) in the antenna unit 30 and the sensor unit 40 in the support unit 22. Furthermore, the numerical value of the pressure in the vitreous body 11 obtained by the sensor unit 40 in the support unit 22 to be described later can be stably transmitted to a reception device (not shown) outside the eye.

In addition, the “outer peripheral part” here is a part of the optical part 21, and an outer peripheral part away from the geometric center of the optical part 21 to the extent that the wearer of the intraocular lens 20 does not visually recognize the antenna part 30. Say that.

As a material of the coil winding 31, a known material may be used as long as it can receive power from the outside using electromagnetic induction and transmit the numerical value of the pressure as the antenna unit 30. good. As an example, it is preferable to use precious metals, particularly gold, in view of conductivity and flexibility in folding.

As for embedding the coil winding 31, a groove for the coil winding 31 is formed in the optical unit 21 in advance, and after the coil winding 31 is fitted into the groove, the same material as the optical unit 21 is formed. The coil winding 31 is embedded with this member to form the antenna unit 30.

In addition, the antenna unit 30 includes at least one electronic module 32 in addition to the coil winding 31. The electronic module 32 has a function of receiving the numerical value of the pressure in the vitreous body 11 transmitted from the sensor unit 40 and further allowing the numerical value to be transmitted to an external receiving device by a wireless method. The electric power at that time is supplied from the outside by the coil winding 31.

In order to perform the above function, the electronic module 32 is in contact with the coil winding 31 having an antenna function. In order to facilitate the contact between the electronic module 32 and the coil winding 31, it is preferable that the coil winding 31 be substantially straight rather than arcuate in plan view in the vicinity of the electronic module 32.

Further, a memory may be provided inside the electronic module 32. This memory stores the pressure value in the vitreous body 11 continuously measured and recorded in real time by the sensor unit 40 described later. These pressure values can be retrieved from this memory at appropriately determined intervals and transmitted to a receiving device outside the eye. A known device can be used as this receiving device.

The electronic module 32 is made of a foldable material. As a result, the size of the intraocular lens 20 can be reduced, and as a result, the wound for inserting the intraocular lens 20 into the lens capsule 8 can be minimized. However, in order to minimize the damage to the electronic module 32, the optical unit should not be present at the folding position (on the line AA ′ in FIG. 2A) when the intraocular lens 20 is folded. It is preferable to arrange the electronic module 32 at 21. For example, as shown in FIG. 2A, it is preferable to arrange the electronic module 32 in a portion of the optical unit 21 in the vicinity of the boundary between the optical unit 21 and the support unit 22.

C) Support part (including sensor part)
In the present embodiment, the support portion 22 is a part of the intraocular lens 20 and is a portion extending outward from the optical portion 21 into an open loop shape and two arms. When the intraocular lens 20 is viewed in plan, as shown in FIG. 2A, the support portion 22 draws a smoothly continuous arc from a portion near the boundary between the optical portion 21 and the support portion 22 to the distal end portion 22c. Has a contour. The optical unit 21 and the support unit 22 are integrally molded. When the intraocular lens 20 is inserted into the capsular bag 8, the film inside the capsular bag 8 comes into contact with the support unit 22, so that the optical unit 21 is brought into the capsular bag 8 via the support unit 22. Will be retained. That is, the support part 22 plays a role of supporting the optical part 21 in the lens capsule 8.

A sensor unit 40 is provided in a portion of the support unit 22 near the boundary between the optical unit 21 and the support unit 22 (hereinafter also referred to as “base 22a”). The sensor unit 40 is not merely for measuring the intraocular pressure as in the prior art, but has a function of measuring the pressure in the vitreous body 11 via the posterior capsule 8b in the lens capsule 8.

<4. Intraocular Lens Usage Method> As shown in FIG. 3 which is an explanatory view showing the usage method of the intraocular lens 20 according to one embodiment of the present invention, the intraocular lens 20 in this embodiment is a lens capsule. When the lens capsule 8 is inserted into the lens capsule 8 (FIGS. 3 (a) and 3 (b)), the lens capsule 8 is kept in a substantially elliptical shape to some extent, but the lens capsule 8 becomes constant by adapting to the intraocular lens 20. The degree is reduced, and the intraocular lens 20 and the lens capsule 8 come into contact with each other (FIG. 3C).

In this embodiment, the sensor unit 40 is provided on the support unit 22 as described above by utilizing the contact between the intraocular lens 20 and the lens capsule 8 (particularly the posterior capsule 8b). By doing so, since the intraocular lens 20 and the lens capsule 8 are in contact with each other, pressure is applied to the sensor unit 40 from the rear capsule 8 b of the lens capsule 8. At this time, the main factor of the pressure applied to the posterior capsule 8b is the pressure in the vitreous body 11 from the positional relationship between the lens capsule 8 and the vitreous body 11. As a result, when the intraocular lens 20 has the above-described configuration, the pressure in the vitreous body 11 is faithfully transmitted to the sensor unit 40 via the posterior capsule 8b of the crystalline lens capsule 8 ( FIG. 3 (d)). A pressure that is the same as or very close to the pressure in the vitreous body 11 can be measured in real time.

As can be seen from FIGS. 2A, 2B, and 2D, the root 22a of the support portion 22 is the end portion of the support portion 22 (when viewed from the center of the optical portion 21 when the intraocular lens 20 is viewed in plan view). And a portion that is relatively close to the center of the optical unit 21. On the other hand, due to the fact that the capsular bag 8 is substantially elliptical in cross-sectional view and the mutual arrangement of the capsular bag 8 and the vitreous body 11, the pressure in the vitreous body 11 is closer to the center of the optical part 21 in the posterior capsule 8b. Is easier to communicate. As a result, by providing the sensor unit 40 in a portion of the support unit 22 that is relatively close to the center of the optical unit 21 (that is, the base 22a), the lens capsule 8 is provided although the sensor unit 40 is not provided in the optical unit 21. The pressure in the vitreous body 11 is more faithfully transmitted to the sensor unit 40 in the support unit 22 through the rear capsule 8b.

In addition, as described above, when the intraocular lens 20 is viewed in plan, the sensor unit 40 is provided in the support unit 22 at a position near the center of the optical unit 21. In addition, when the intraocular lens 20 is viewed in cross-section, it is preferable to provide the sensor unit 40 on the support portion 22 on the back capsule 8b side. That is, the sensor unit 40 is provided on the posterior capsule 8b side in the thickness direction. By doing so, when the intraocular lens 20 is inserted into the crystalline lens capsule 8, the sensor unit 40 can be arranged so as to be positioned in the vicinity of the posterior capsule 8b. If it becomes so, the pressure in the vitreous body 11 will be further faithfully transmitted to the sensor part 40, and the effect in this embodiment will be amplified.

Note that, as described above, the sensor unit 40 includes the sensor 41 for measuring the pressure in the vitreous body 11 and the member 42 covering the periphery thereof. In the case of the present embodiment, the sensor 41 is a sensor 41 that is the main body of the sensor unit 40 and is an electronic module (in order to distinguish it from the electronic module 32 in the antenna unit 30, the 41 ").

The sensor 41 includes a pressure-sensitive element for sensing pressure applied from the posterior capsule 8b (that is, pressure in the vitreous body 11), and an electric circuit for transmitting the measured pressure to the antenna unit 30. I have.

Further, the surrounding member 42 is a material constituting the support portion 22. That is, in the present embodiment, the sensor 41 is embedded in the base 22 a of the support portion 22.

In addition, as this sensor 41, if it is a pressure sensor which can measure the pressure applied from the back capsule 8b in real time, you may use a well-known pressure sensor. Further, similarly to the electronic module 32 in the antenna unit 30, a memory may be provided inside the sensor 41.

As for the embedding of the sensor 41 in the support portion 22, a hole for the sensor 41 is formed in the support portion 22 in advance like the coil winding 31 in the antenna portion 30, and the sensor 41 is fitted into the hole. Then, the sensor 41 is embedded with a member made of the same material as the support portion 22 to form the support portion 22.

As described above, soft acrylic is used for the optical unit 21 and soft acrylic and PMMA are used for the support unit 22. Here, PMMA, which is a hard material, is used in the vicinity of the boundary between the optical unit 21 and the support unit 22 in the support unit 22. And the sensor 41 is embedded in the part which consists of this PMMA.

In this way, not only the effect of protecting the sensor 41 from an impact can be obtained, but also the “displacement amount is relatively small” that is a feature of the present embodiment can be more reliably performed. The effect of can be further exhibited. That is, by configuring the periphery of the sensor 41 with PMMA, which is a hard material, the amount of displacement when an impact is applied to the intraocular lens 20 can be made smaller than in the case of a soft material. As a result, in the support portion 22 with a small displacement amount, the displacement amount can be further reduced, and the contact between the posterior capsule 8b and the sensor portion 40 can be maintained almost always. Thus, the pressure in the vitreous body 11 that applies pressure to the optic nerve 15 can be constantly observed in real time.

In addition, in this embodiment, PMMA is used also for the front-end | tip part 22c in the support part 22 besides the base 22a of the support part 22. FIG. In this way, after the intraocular lens 20 is folded, when the intraocular lens 20 is returned to the original shape again in the crystalline lens capsule 8, due to the difference in hardness and the adhesive force between the tip 22c and the optical part 21 The folding is easily released.

The portion of the support portion 22 other than the tip portion 22c and the root 22a (hereinafter also referred to as “support portion main body 22b”) is made of soft acrylic. By configuring the support portion 22 in this manner, the support portion 22 is also folded when the intraocular lens 20 is folded, but breakage of the support portion 22 at the time of folding can be suppressed. Further, <6. As described in Modification>, it is possible to prevent the support portion 22 from being damaged when the intraocular lens 20 is a sewing type.

Further, although the support portion main body 22b and the tip end portion 22c are separated from each other, the tip end portion 22c and the support portion main body 22b are separated from each other when the arc line having the center of the optical unit 21 is concentric. It is divided as a line. Furthermore, when the support part main body 22b and the base 22a draw the circular arc line which makes the center of the optical part 21 concentric, the said circular arc line is divided as a boundary line.

Further, the base 22a of the support portion 22 is formed in a mountain-like shape toward the geometric center of the optical portion 21 when viewed in plan, and is connected to the optical portion 21 at the widest portion. With respect to the base 22a, the support portion main body 22b extends from the base 22a to the outside so as to draw a circular arc obliquely outward. And the front-end | tip part 22c part is formed a little wider than the support part main body 22b.

Also, the tip 22c is rounded so as not to damage the lens capsule 8 even if it contacts the lens capsule 8. Further, the tip 22c, the base 22a, and the support body 22b constituting the support part 22 are structurally integrated only in the materials of the respective parts.

Further, as shown in FIGS. 2B, 2C, and 2D, the main surface of the support portion 22 is continuous between the optical portion 21 and the support portion 22 when viewed in cross section. It may have a surface shape. On the other hand, on the rear surface 20b side, a stepped portion 21a may be provided at the boundary portion between the optical unit 21 and the support unit 22 as described above. In addition, as shown in FIG. 2B, the cross-sectional shape of the support portion 22 initially extends substantially horizontally from the center of the optical portion 21 outward, and thereafter has an inclination toward the front surface 20a. Then, it may extend substantially horizontally. With this configuration, when the intraocular lens 20 is inserted into the lens capsule 8, the support unit 22 can suppress the optical unit 21 from being excessively displaced in the optical axis direction.

<3. Manufacturing method of intraocular lens>
Then, the manufacturing method of the intraocular lens 20 which concerns on the 1st Embodiment of this invention is demonstrated. The manufacturing method of the intraocular lens 20 can be mainly divided into four steps. Hereinafter, it demonstrates according to the flow of a process using FIG.

(First step)
First, as shown in FIG. 4A, an annular outer hard material portion 201 is obtained by a known molding method using, for example, PMMA (hard material). Then, an inner hard material portion 202 is formed inside the outer circular hole 101 ′ with the outer circular hole 101 ′ interposed therebetween. Then, an inner circular hole 102 ′ is formed inside the inner hard material portion 202 with the inner hard material portion 202 interposed therebetween. The outer hard material portion 201, the outer circular hole 101 ′, the inner hard material portion 202, and the inner circular hole 102 ′ are arranged concentrically.

(Second step)
Next, as shown in FIG. 4B, for example, a soft acrylic raw material solution is injected into the outer circular hole 101 ′ and the inner circular hole 102 ′ after polymerization to complete the polymerization. Thereby, the outer side soft material part 101 of planar view donut shape and the inner side soft material part 102 of circular shape by planar view are formed in the place where outer side circular hole 101 'and inner side circular hole 102' existed. As a result, the intermediate member 300 having a structure in which the outer hard material portion 201 and the inner hard material portion 202 and the outer soft material portion 101 and the inner soft material portion 102 are integrated is obtained.

(Third step)
Next, as shown in FIG. 4C, the surface shape of the intermediate member 300 is adjusted according to the surface shapes of the optical part 21 and the support part 22 to be completed. Specifically, a common cutting tool 61 for surface machining and grooving (for example, the curvature R of the tip is 0.2, the inclination from the tip is 30 °, and the radius of the portion without the tip is 0. 1), a surface forming process such as milling is performed on the front and rear surfaces of the intermediate member 300. Thereby, the surface shape of the intermediate member 300 is adjusted according to the convex curved surface of the optical unit 21, the slope of the root portion of the support unit 22, and the other flat surface. That is, the curved shapes of the optical surfaces of both the front surface 20a and the rear surface 20b of the optical portion 21, and the surface shapes of the two support portions 22 located on both the front surface 20a side and the rear surface 20b side of the optical portion 21. Form. Thereby, the disc-shaped intermediate member 300 reflecting the shape of the front surface 20a and the rear surface 20b of the intraocular lens 20 is obtained.

(4th process)
Then, together with the third step, the precision lathe device equipped with the grooving tool 62 is used to adjust the shape of the intermediate member 300 in accordance with the outline of the optical part 21 and the support part 22 when viewed in plan. The intermediate member 300 is grooved, and the intraocular lens 20 is cut out from the intermediate member 300 along the contour of the intraocular lens 20 to be completed. Specifically, the circle is centered on the optical axis of the optical unit 21 and passes through a circle passing through the boundary between the region serving as the optical unit 21 and the region serving as the two support units 22 in the intermediate member 300. The first intermediate member is grooved by a precision lathe equipped with a grooving tool 62. Then, an unnecessary portion as the intraocular lens 20 is removed from the intermediate member 300 by performing an outer shape process such as a milling process on the intermediate member 300.

This grooving process can be performed in a series of steps following the above-mentioned surface forming process, if a common cutting tool 61 for surface processing and grooving is used as the cutting tool in the surface forming process. The diameter of the grooving tool 62 is 1.5 mm. The grooving process may be performed by the milling device when the contour shape is formed by a milling device to be described later without performing the lathe processing.
Thereafter, polishing is performed on necessary portions.

Through the above process, the one-piece type intraocular lens 20 is obtained. However, not limited to the above manufacturing method, for example, all of the first to fourth steps described above may be performed simultaneously by a cast mold manufacturing method. Alternatively, the first step to the second step may be simultaneously performed by a cast mold manufacturing method, and then the third step to the fourth step may be performed. Of course, other known methods (for example, a spin cast manufacturing method or a lace cut manufacturing method) may be used.

<4. How to use intraocular lens>
There are two forms of use of the intraocular lens 20. One is a case where the intraocular lens 20 is used as a non-sewn type. The other is a case where the intraocular lens 20 is used as a sewing type. In the present embodiment, a method of using the intraocular lens 20 when the intraocular lens 20 is used as a non-sewn type will be described with reference to FIG. The sewing mold is described in <6. Modification> will be described.

Prior to inserting the intraocular lens 20 into the eye, a wound is formed on the surface of the eyeball 1 prior to that, and the lens (the lens cortex, the lens nucleus) is removed through the wound (FIG. 3A).

The cataract lens is removed from the capsular bag 8 by forming a small circular opening (CCC: Continuous Curvular Capsular Hexis or Continuous Circular Capsule Hexis) 19 in the anterior capsule 8a of the capsular bag 8 by ultrasonic emulsification PEA) may be used.

On the other hand, the intraocular lens 20 is folded small in advance. At this time, the intraocular lens 20 is folded in such a manner that the optical part 21 is folded in two along the line A-A ′ of FIG. 2A so that the two support parts 22 do not overlap each other. At this time, the support portion 22 is also folded at the base 22 a, and the folded support portion 22 is wrapped with the optical portion 21.

Specifically, the intraocular lens 20 is inserted into the injector 50 while being folded. The injector 50 is a surgical instrument used for inserting the intraocular lens 20 into the eye.

Next, the intraocular lens 20 is inserted through the circular opening 19 by causing the distal end portion 51 of the injector 50 to which the intraocular lens 20 is attached to face the circular opening 19 of the eyeball 1 and pushing the intraocular lens 20 from the injector in this state. Is inserted into the eye (the lens capsule 8). At this stage, the intraocular lens 20 is in a folded state.

Next, the folded intraocular lens 20 is developed into the original shape using an insulator or the like (FIG. 3B). At this time, the capsular bag 8 becomes familiar with the intraocular lens 20, whereby the capsular bag 8 is reduced to a certain degree, and the intraocular lens 20 and the capsular bag 8 come into contact with each other (FIG. 3C). Thereby, the support part 22 extended from the optical part 21 contacts the back capsule 8b of the crystalline lens capsule 8, and the optical part 21 is supported at an appropriate position using this contact pressure.

By this contact, the pressure in the vitreous body 11 is transmitted to the support portion 22. In the present embodiment, this pressure is transmitted by the sensor unit 40 at the base 22 a of the support unit 22. The sensor 41 of the sensor unit 40 measures the pressure in the vitreous body 11 via the posterior capsule 8b (and the member 42 covering the periphery of the sensor 41), and transmits the value to the electronic module 32 of the antenna unit 30. (FIG. 3 (d)). The pressure value is transmitted from the electronic module 32 to the outside in real time.
The circular opening 19 may be closed by a known method after the operation.

<5. Advantages of the embodiment>
In the intraocular lens 20 according to the present embodiment, the intraocular pressure is not converted from the “displacement amount of the cornea 2” as in the prior art, but the “pressure in the posterior capsule 8b” that faithfully reflects the pressure in the vitreous body 11. Is measuring. In other words, in this embodiment, absolute values for determining the possibility of progression of glaucoma with respect to what is obtained as an absolute value parameter for any patient (pressure in the vitreous body 11 in this embodiment). It has succeeded in setting a value standard.

Moreover, since the antenna unit 30 and the sensor unit 40 are provided in the intraocular lens 20, the pressure in the vitreous body 11 can be measured in real time. In addition, the pressure in the vitreous body 11 that directly compresses the optic nerve 15 can be measured via the posterior capsule 8b without converting the amount of displacement of the cornea 2 to the pressure. Therefore, a value that faithfully reproduces the pressure in the vitreous body 11 can be measured by the sensor unit 40. Further, since the intraocular lens 20 is always present in the wearer's eye, it is possible to grasp in real time whether the pressure in the vitreous body 11 of the wearer is normal or abnormal, and this pressure tends to increase. Can quickly identify signs of glaucoma.

Furthermore, in this embodiment, in order to accurately transmit the pressure in the vitreous body 11 to the sensor unit 40 in real time, the sensor unit 40 is connected to the support unit 22 so that the sensor unit 40 is always or almost always in contact with the posterior capsule 8b. 40 is arranged. In addition, an antenna unit 30 is provided in the optical unit 21. That is, the role is divided such that the pressure is measured by the support portion 22 and the pressure is transmitted to the outside by the optical portion 21.

In the optical unit 21, the coil winding 31 in the antenna unit 30 is arranged on the outer periphery of the optical unit 21, so that a certain length in the coil winding 31 is ensured even if the intraocular lens 20 is downsized. can do. As a result, the numerical value of the pressure in the vitreous body 11 can be transmitted and received stably.

And in the support part 22, it can suppress that the sensor 41 displaces to an optical axis direction by arrange | positioning the sensor part 40 to the support part 22. FIG. As a result, the contact state of the lens capsule 8 with the posterior capsule 8b can be constantly or almost always maintained, and the pressure in the vitreous body 11 can be measured in real time.

As a result, the intraocular lens 20 according to the present embodiment can suppress the risk of progression of glaucoma by measuring in real time a pressure that is the same as or very close to the pressure in the vitreous body 11.

<6. Modification>
The present invention is not limited to the contents of the above-described embodiment, and can be appropriately changed without departing from the gist thereof.

(Configuration of intraocular lens)
In the present embodiment, the integrated intraocular lens 20 in which the optical unit 21 and the support unit 22 are integrated from the stage of the intermediate member has been described. On the other hand, the application range of the present invention extends to a multi-piece type intraocular lens 20 which is not an integral type. That is, even in the multi-piece type intraocular lens 20, the sensor unit 40 is provided in the support unit 22, the antenna unit 30 is provided in the optical unit 21, and the pressure in the vitreous body 11 is applied to the posterior capsule 8 b by the sensor unit 40. If the measurement is performed via the above, the effect of the present embodiment is obtained.

In this embodiment, the step portion 21a is provided at the boundary portion between the support portion 22 and the optical portion 21, but the step portion 21a is made small so that the posterior capsule 8b can easily come into contact with the sensor portion 40 of the support portion 22. Alternatively, a configuration in which the step portion 21a is not provided may be employed.

(Material of optical part)
The optical unit 21 is preferably made of a soft material that allows the optical unit 21 to be folded. The term “foldable” described here is used to mean that the intraocular lens 20 including the optical unit 21 can be folded in at least two. Therefore, the soft material constituting the optical unit 21 may be a material having a high flexibility enough to fold the optical unit 21. As specific examples other than soft acrylic, soft materials such as silicone resin, acrylic resin, hydrogel, and urethane resin can be used.

On the other hand, of course, the present invention may be applied to an intraocular lens that does not require folding. In that case, PP (polypropylene), polyimide, PMMA, or the like, which is a hard material, may be used, and a known material may be used as long as it can be used as the optical unit 21. However, in that case, since the wound to the cornea 2 becomes large, it is preferable to apply the present invention to a foldable intraocular lens.

(Optical part shape)
In the present embodiment, the case where both the front surface 20a and the rear surface 20b of the intraocular lens 20 (particularly the optical unit 21) have a convex shape has been described, but one or both surfaces have a concave shape. Of course, the idea of the present invention can be applied.

(Optical part dimensions)
The optical unit 21 in the present embodiment is formed in a convex lens shape having a circular shape in plan view. The diameter of the optical unit 21 may be set to any size as long as it is a size suitable for inserting the intraocular lens 20 into the lens capsule 8 in the eye. To describe a specific dimension setting example, the diameter D of the optical unit 21 is preferably set in the range of 5 mm to 7 mm, more preferably 6 mm. What is necessary is just to set the thickness of the optical part 21 according to a desired refractive index.

(Support material)
In the present embodiment, the support portion 22 is made of a material having a hardness different from that of the optical portion 21, but the material is not limited in order to embody the idea of the present invention. However, considering that the optical unit 21 is supported in the lens capsule 8, it is preferable that the support unit 22 (at least the base 22a) is made of a hard material in order to stably arrange the optical unit 21. If a specific example is given as a material of the support part 22 other than PMMA, hard materials, such as a polypropylene and a polyamide, can be used. Moreover, the whole support part 22 may be comprised with the same material, the front-end | tip part 22c, the support part main body 22b, and the base 22a may be comprised with a different material, respectively, and those combinations are comprised with the same material. You may do it.

Furthermore, in order to have a certain strength and flexibility with respect to the base 22a in order to suppress breakage when the intraocular lens 20 is folded, the base 22a uses a mixture of a hard material and a soft material. May be.

Further, the content ratio of the hard material may be changed (for example, decreased) from the optical part 21 side to the tip side of the base 22a, or the content ratio of the hard material is changed in the thickness direction of the support part 22 ( For example, it may be reduced). By doing so, the flexibility of the base portion 22a on the optical unit 21 side is further increased, and breakage during folding can be further suppressed.

(Shape of support part)
The support portion 22 in the present embodiment is formed in an open loop shape and an arm shape extending outward, and two of them are formed. On the other hand, the support portion 22 applied to the present invention may have other shapes. Specific examples include a support unit 22 that is not an open loop but a closed loop, a flat support 22 that is not an arm, or one or three or more support units 22 instead of two. Also good.

(Support part dimensions)
Although there is no particular limitation on the size of the support portion 22 in the present embodiment, when the size of the standard lens capsule 8 is taken into consideration, the diameter of the entire intraocular lens 20 is reduced when the intraocular lens 20 is inserted into the lens capsule 8. The total length of the support portion 22 is preferably set so as to be about 10 mm.

(Coloring tip)
You may comprise the front-end | tip part 22c in the support part 22 with PMMA containing the well-known coloring agent. By doing so, when the intraocular lens 20 is folded and inserted into the crystalline lens capsule 8 and the intraocular lens 20 is returned to the original shape again, it is easy for the operator who performs the operation to visually recognize the distal end portion 22c. As a result, the surgeon can easily pick the distal end portion 22c, and the operation can be performed smoothly. In the present embodiment, there are two support portions 22, but each tip portion 22 c may be colored with a different color. Then, even during the operation, in the intraocular lens 20, it can be easily identified which is the front surface 20a or the rear surface 20b. Of course, a known colorant may be contained in the portion other than the tip portion 22c.

(Sewing lens)
In the present embodiment, the intraocular lens 20 when the intraocular lens 20 is a non-sewn type has been described. Hereinafter, the intraocular lens 20 when the intraocular lens 20 is a sewn type will be described.

First, the sewn-type intraocular lens 20 holds the optical unit 21 in an appropriate position by fixing the support unit 22 to the eyeball 1 with a suture while the intraocular lens 20 is housed in the crystalline lens capsule 8. That is, the type of intraocular lens 20. Then, a hole may be provided in the distal end portion 22c so that the suture thread passes through the intraocular lens 20. Hereinafter, an example of a hole is shown.

The hole is formed on the extending end side of the support portion 22 so as to penetrate in the thickness direction of the support portion 22. Further, the hole is formed as a circular through hole in plan view. This hole corresponds to a locking portion that allows the suture used for fixing the support portion 22 to the eyeball 1 to be wound and prevents the wound suture from being displaced. The hole may be provided in the tip portion 22c, or may be provided in other portions.

Even in the case where the intraocular lens 20 is sewn, in the present embodiment, the support body 22b is made of soft acrylic, so that the optical part 21 can be elastically deformed in the radial direction. As shown in FIGS. 2 (a) and 2 (b), the support portion main body 22b extends as a whole elongated. And the material itself which comprises this has a moderate softness | flexibility. For this reason, when the external force which goes to the center of the optical part 21 through the front-end | tip part 22c is received, the support part main body 22b becomes a structure which can elastically deform in the radial direction of the optical part 21 according to this external force.

Furthermore, in this embodiment, it is preferable that the front-end | tip part 22c provided with the hole is comprised with the hard material harder than the support part main body 22b. This is because, when the suture thread is tied to the hole, even if the suture thread is tied up to some extent, the possibility that the portion (tip portion 22c) is torn off can be suppressed.

(Intraocular lens holder)
When the intraocular lens 20 according to the present embodiment is mounted in the crystalline lens capsule 8, it is known that maintaining the circular shape of the crystalline lens equator contributes to stabilization of lens fixation. Therefore, when attaching the intraocular lens 20 into the crystalline lens capsule 8, an auxiliary tool (an intracapsular holder) for attaching a lens called an intracapsular ring may be used. However, even when the intraocular lens 20 is fitted into the intracapsular ring, it is necessary to configure the intraocular lens 20 and the intracapsular ring so that the sensor unit 40 and the posterior capsule 8b in the support unit 22 can maintain a contact state. There is.
Even when the capsular bag 8 itself is excised, the intraocular lens 20 may be attached to a holder that replaces the capsular bag 8. Specifically, in the sensor unit, the pressure in the vitreous body is measured by bringing the sensor unit 40 and the vitreous body 11 into direct contact rather than through the posterior capsule 8b. A specific configuration in this case will be described in [Appendix] described later.

(Number of electronic modules / sensors)
In the present embodiment, the case where the electronic module 32 of the antenna unit 30 and the sensor 41 of the sensor unit 40 are provided one by one has been described. In particular, one sensor 41 may be provided in each support portion 22.

(Embedded electronic module / sensor)
In this embodiment, in the embedding of the electronic module 32 of the antenna unit 30 and the sensor 41 of the sensor unit 40, the case where the embedding is performed with the material composing the optical unit 21 and the material composing the support unit 22, respectively. It was. On the other hand, an embedding member may be prepared separately, or a material different from the material constituting the optical unit 21 or the support unit 22 may be prepared separately for embedding.

Further, instead of embedding with an embedding member, a gap for the electronic module 32 and the sensor 41 is provided in the optical unit 21 and the support unit 22 in advance, and the electronic module 32 and the sensor 41 are connected to the optical unit 21 and the support unit 22. It is also conceivable that, after being housed in, the lid in which the electronic module 32 and the sensor 41 are housed is covered using a separately prepared lid. However, it is necessary to select a material that has a slight influence on the wearer's eyes, whether it is the lid or the above-described embedding member.

(How to wind coil winding)
If it functions as the antenna unit 30, there is no limitation on the winding method of the coil winding 31, but for example, the coil windings 31 are adjacent to each other in the radial direction of the optical unit 21. The antenna portion 30 may be formed in a planar and annular shape by winding the wire around the wire. Alternatively, the antenna unit 30 may be formed by stacking the planar antenna units 30 to form a plurality of planes composed of the coil windings 31.

(Sensor position)
In this embodiment, the sensor part 40 gave the example provided in the part of the support part 22 near the boundary between the optical part 21 and the support part 22. Moreover, when the intraocular lens 20 was inserted into the capsular bag 8, an example was given in which the sensor unit 40 is provided on the support unit 22 so that the sensor unit 40 is positioned in the vicinity of the posterior capsule 8 b. On the other hand, if the sensor 41 can sense the pressure in the vitreous body 11 via the posterior capsule 8b, the sensor unit 40 may be arranged at a location of the support unit 22 other than the above. If the above sensing can be ensured, the sensor unit 40 may be provided at the tip 22c of the support unit 22. Further, if the pressure in the vitreous body 11 can be accurately sensed via the posterior capsule 8b, the sensor unit 40 may be provided on the anterior capsule 8a side in the thickness direction.

Hereinafter, other preferable modes will be additionally described.
[Appendix 1]
An intraocular lens comprising an optical part having a predetermined refractive power and a support part that supports the optical part,
The support part is provided with a sensor part for measuring the pressure in the vitreous body by contacting with the vitreous body,
An intraocular lens, wherein the optical unit is provided with an antenna unit that transmits the pressure measured by the sensor unit to the outside.

DESCRIPTION OF SYMBOLS 1 Eyeball 2 Cornea 3 Sclera 4 Conjunctiva 5 Anterior chamber 6 Iris 7 Pupil 8 Lens capsule 8a Front capsule 8b Rear capsule 9 Ciliary zonule
DESCRIPTION OF SYMBOLS 10 Ciliary epithelium 11 Vitreous body 13 Retina 14 Choroid 15 Optic nerve 16 Blind spot 17 Fovea 18 Corner angle 18a Trabecular band 19 Circular opening 20 Intraocular lens 20a Front surface 20b Rear surface 21 Optical part 22 Support part 22a Base 22b Support part main body 22c Tip part 30 Antenna part 31 Coil winding 32 Electronic module 40 Sensor part 41 Sensor 42 Surrounding member 50 Injector 51 Injector tip part 61 Common tool 62 Grooving tool 101 Outer soft material part 101 'Outer circular hole 102 Inner soft Material part 102 ′ inner circular hole 201 outer hard material part 202 inner hard material part 300 intermediate member

Claims

An intraocular lens comprising: an optical part having a predetermined refractive power; and a support part that supports the optical part in the lens capsule.
The support part is provided with a sensor part for measuring the pressure in the vitreous through the posterior capsule in the crystalline lens capsule,
An intraocular lens, wherein the optical unit is provided with an antenna unit that transmits the pressure measured by the sensor unit to the outside.
The intraocular lens according to claim 1, wherein the sensor unit is provided in a portion of the support unit near a boundary between the optical unit and the support unit.
The sensor part is provided in the support part so that the sensor part is positioned in the vicinity of the posterior capsule when an intraocular lens is inserted into the crystalline lens capsule. Intraocular lens.
The optical part is formed of a soft material,
In the support part, at least part of the vicinity of the boundary between the optical part and the support part is formed of a hard material compared to the soft material,
The intraocular lens according to any one of claims 1 to 3, wherein the sensor unit is provided on at least a part of the lens.