KR20210050706A - Intraocular pressure measuring device - Google Patents

Abstract

The present invention relates to an intraocular pressure measuring device using a mechanoluminescence material in which mechanical deformation results in luminescence. The present invention includes: a deformation film; a deformation generation unit applying a force to the deformation film so that the deformation film is deformed; and a measuring sensor detecting the degree of the deformation of the deformation film attributable to the deformation generation unit. The deformation film is made in the form of an eyeball-attachable thin film using a composite material that is a mixture of a flexible resin material and an optomechanical luminescence material emitting light in response to mechanical deformation application. By adopting the mechanoluminescence film that emits light in response to a mechanical surface change, a considerable accuracy enhancement can be achieved as compared with existing Goldmann and Pascal tonometers. In addition, a novice as well as an expert can perform measurement, a sudden eye disease can be easily prevented at home by anyone, and thus eye health management can be improved substantially.

Description

Intraocular pressure measuring device

The present invention relates to an intraocular pressure measuring device, and more particularly, to an intraocular pressure measuring device in which a Mykeno luminescent material that emits light due to mechanical deformation is used.

Sight is the sense that a person relies on most in life. If you lose your eyesight, your daily life can stop instantly. Glaucoma is a disease that causes you to gradually lose your eyesight. Glaucoma is a disease that accounts for the highest proportion of the three causes of blindness.

In particular, normal-tension glaucoma is a disease in which the anterior angle is open in the normal range (less than 21mmHg), and characteristic glaucoma-like optic nerve damage and resulting visual field defects appear. The characteristic feature is that there are almost no subjective symptoms because the intraocular pressure is not high. Because visual field changes are also gradually progressing, patients themselves are not aware of the disease until the end of glaucoma is in most cases. Peripheral vision decreases as the disease progresses. At the end, it shows a view as if seeing objects through a tunnel, and it is a terrifying disease that can lead to blindness if it progresses further.

Normal-tension glaucoma is difficult to diagnose early because there are few subjective symptoms. So, rather than going to a hospital because of suspicion of glaucoma, there are many cases of other ophthalmic symptoms or accidental discovery during examination and treatment by visiting an ophthalmologist for a medical examination.

A visual field test is essential to evaluate the function of the optic nerve. This is because glaucoma progresses from peripheral vision impairment to blindness. Visual field examination is very important not only in the diagnosis of glaucoma, but also in the progression and follow-up of the disease.

In addition, as glaucoma progresses, the optic nerve papillae shows glaucoma-related damage, so an optic nerve papillary test is necessary, and a retinal nerve fiber layer test to measure the phenomenon that the thickness of the retinal nerve fiber layer becomes thinner as glaucoma progresses is a useful test for diagnosis.

But above all, the most important factor in glaucoma is intraocular pressure (IOP). In normal-tension glaucoma patients, the intraocular pressure is measured in the normal range, but it is also very important to measure intraocular pressure because it is a risk factor for the progression of glaucoma.

In order to prevent the risk of developing glaucoma, it is essential to monitor intraocular pressure through a tonometer. As can be seen in Fig. 1a, the eye, a human visual system composed of the cornea (C), sclera (D), iris (B), lens (A), and ciliary band fibers, is a sensory organ that receives visual information and transmits it to the brain. . There are two body cavities in the eye, one is the posterior chamber surrounded by the sclera (D) and the lens, the other is the cornea (C), the iris (B) and the anterior chamber surrounded by the lens. These two rooms are filled with aqueous fluids. Glaucoma is caused by damage to the optic nerve due to loss of retinal ganglion cells (RGC).

Elevated intraocular pressure is the most important symptom among various risk factors related to eye health. It is primarily associated with increased water pressure due to an increase in aqueous fluid in the eye. In a normal person, aqueous body fluids are released through the trabecular stem to maintain adequate intraocular pressure. However, in the case of glaucoma patients, the trabecular stem malfunctions due to some problems, the aqueous body fluid is no longer discharged, and the intraocular pressure increases, which can damage the optic nerve, causing glaucoma. As can be seen in FIG. 1 b, the normal intraocular pressure is 10 to 21 mmHg (average 15 mmHg), the difference in intraocular pressure between the right and left eyes is less than 3 mmHg, and the intraocular pressure of glaucoma patients is 21 mmHg or more. Statistically, the 21 mmHg value is widely considered to differentiate between normal and abnormal intraocular pressure. Typically, glaucoma can be prevented by detecting and treating abnormal pressure increases through regular intraocular pressure monitoring. Therefore, early diagnosis of glaucoma is important.

Among the conventional measuring equipment related to the measurement of intraocular pressure, the Goldman tonometer is widely used as a standard diagnostic method. The Goldman tonometer is a measuring instrument based on Applanation Tonometry, which applies Imbert-Fick's law that the internal pressure is equal to the external force divided by the area of the applanation plane. The principle of Imbert-Fick's law is that the force required to flatten or protrude the local surface of a sphere is equal to the product of the pressure inside the sphere and the applied area. At this time, when a certain local area is flattened, the pressure of the eye is determined from the stiffness of the cornea (C) and the force applied so as to cancel the force exerting deformation on the cornea (C).

The Goldman tonometer can measure relatively accurate intraocular pressure, but it may not be accurate when the surface of the cornea (C) is not normal, and may be affected by the thickness of the cornea (C) or the concentration of fluorescent staining. Among them, when the thickness of the cornea (C) is thin, it is measured to be lower than the actual intraocular pressure, and when the collagen of the cornea (C) increases and becomes thick, it is measured to be higher. However, when the secondary thickness increases due to corneal (C) edema, the results are measured lower than the actual intraocular pressure.

The Goldman tonometer is a contact type, while the Air Puff tonometer is a non-contact type tonometer. However, although the Goldman tonometer is more accurate than other tonometers, it requires anesthesia and has a disadvantage in that it requires measurement by an ophthalmologist because it is difficult to measure.

The Pascal tonometer (dynamic contour tonometry, PAS CALㄾ) is a tonometer that is designed not to cause deformation of the cornea (C) without flattening the cornea (C) by being mounted on a slit lamp microscope and not affected by the characteristics of the cornea (C). The silver is made as close as possible to the curvature of the cornea (C), so that the intraocular pressure is measured directly by contacting the cornea (C). When this tonometer is in contact with the apex of the cornea (C), there is little change in the shape of the surface of the cornea (C), and theoretically, the pressure in all directions acting within the cornea (C) is embedded in the contact part of the cornea (C). It is directed evenly to the sensor.

However, with Pascal tonometers, measuring intraocular pressure is difficult compared to previously designed tonometers. For accurate intraocular pressure measurement, the sensor tip must be in contact with the patient's cornea (C) for at least 4 to 5 seconds compared to the Goldman applanation tonometer, and if the patient moves the eye or the head while measuring the intraocular pressure, the correct intraocular pressure Can not be measured.

The air puff tonometer has been regarded as a quick and simple method for measuring intraocular pressure in children and other non-compliant patient groups, but it is not considered an accurate method of measuring intraocular pressure. Therefore, there is a desperate need for new alternatives that are more accurate, reliable and easier to handle.

Unexamined Patent Publication No. 10-2019-0074637 (Publication date: 2019.06.28.)

Accordingly, the present invention provides an intraocular pressure measurement device capable of remarkably increasing accuracy compared to a conventional Goldman tonometer or Pascal tonometer, and capable of measuring even a beginner who is not an expert, so that anyone can easily prevent eye diseases that may occur unexpectedly at home. I want to provide.

In order to achieve this object, the intraocular pressure measurement device according to the present invention includes a deformable film made of a flexible material, a deformation generating unit applying force to the deformable film so that deformation occurs in the deformed film, and a deformable film generated by the deformation generating unit. It is composed of a measurement sensor that detects the degree of deformation, and the deformable film is a composite material in which a photomechanical luminescent material and a flexible resin material having the characteristics of emitting light when mechanical stimulation is applied, and in the form of a thin film that can be attached to the eyeball. It is manufactured and characterized in that it is a Mykeno light-emitting film 10 that causes light emission in response to a mechanical change of the surface.

Here, the Mykeno light-emitting film 10 is preferably formed in a curved surface having the same curvature as the outer surface of the eyeball.

Further, the deformation generating unit is preferably a micro air blower 24 that blows air onto the surface of the Mykeno light-emitting film 10 to apply a fine deformation to the surface of the Mykeno light-emitting film 10.

The measurement sensor for detecting the degree of deformation is preferably a photometric sensor 23 that receives and amplifies microscopic visible light generated by microscopic deformation of the surface of the Mykeno light-emitting film 10 to measure the intensity of visible light.

Here, preferably, the Mykeno light-emitting film 10, the deformation generating unit, and the photometric sensor 23 are installed on the frame 30 made to be mounted on the curvature of the face.

At this time, the Mykeno light-emitting film is preferably attached to the loading jig 21 installed on the frame 30 so that the Mykeno light-emitting film 10 is held in a spherical shape and is held in a sliding manner and can be brought into contact with the eyeball by moving forward or backward in a sliding manner. (10) is installed.

In this case, the loading jig 21 is preferably connected to the circumference of the Mykeno light-emitting film 10 or both sides of the Mykeno light-emitting film 10, and has an elastic support member 22 having a greater elasticity than the Mykeno light-emitting film 10. ) To hold the Mykeno light-emitting film 10.

The intraocular pressure measurement device according to the present invention can significantly increase accuracy compared to the conventional Goldman tonometer or Pascal tonometer, and can be measured by beginners, not experts, so that anyone can easily prevent eye diseases that may occur at home. There is an effect that can dramatically improve eye health management.

1A is a cross-sectional view showing each configuration of an eyeball;
1B is a graph comparing normal intraocular pressure and glaucoma intraocular pressure,
Figure 2a is a cut-away perspective view of a spherical shell modeling the cornea (C) and sclera (D),
2B is a cut-away perspective view of a viscous pressurized fluid modeling a vitreous body fluid,
Figure 2c is a graph showing that a pressure of 330 kPa is applied for 40 ms,
Figure 2d is a cross-sectional view showing that the spherical shell of Figure 2a is deformed under various pressures;
Figure 2e is a graph showing the strain of the spherical shell at various pressures of Figure 2a,
3 is a graph showing a material and structure photograph and wavelength-luminosity and XRD pattern of the Mykeno light-emitting film,
4 is a conceptual diagram showing the basic configuration of an intraocular pressure measuring apparatus according to the present invention,
5 is a graph showing that two peaks are observed at each pressure,
6 is a graph showing the relationship between the optical signature and the pressure,
7 is a perspective view showing an apparatus for measuring intraocular pressure according to an embodiment,
Figure 8 is a plan view of Figure 7;
9 is a partial plan view showing a process in which the Mykeno light-emitting film is seated on the surface of the eyeball;
10 is a table showing the behavioral characteristics of a spherical shell and a viscous fluid model,

Specific structural or functional descriptions presented in the embodiments of the present invention are exemplified only for the purpose of describing the embodiments according to the concept of the present invention, and embodiments according to the concept of the present invention may be implemented in various forms. In addition, it should not be construed as being limited to the embodiments described in the present specification, and should be understood to include all modifications, equivalents, and substitutes included in the spirit and scope of the present invention.

Hereinafter, the present invention will be described in detail with reference to the accompanying drawings.

First, 1. a brief description of the configuration of the intraocular pressure measuring device according to the invention, and in turn 2. the Mykeno light-emitting film 10 used in the invention, and the Mykeno light-emitting film used in the actual experiment for the test of the present invention After explaining the manufacturing process of (10), the modeling method for the experiment, and the experimental result, 3. a specific additional embodiment of the present invention will be described with reference to the drawings.

As shown in FIG. 4, the intraocular pressure measuring device according to the present invention includes a deformable film made of a flexible material, a deformation generating unit applying force to the deformed film so that deformation occurs in the deformed film, and a deformed film due to the deformation generating unit. It consists of a measurement sensor that detects the degree of deformation that is being made.

Here, the deformable film is a composite material in which a photomechanical luminescent material and a flexible resin material having a characteristic that emit light when mechanical deformation occurs is mixed with each other, and is produced in the form of a thin film that can be attached to the eye, and emits light in response to mechanical changes of the surface This is the Mykeno light-emitting film 10 that is caused.

The photomechanical luminescent material is a material in which light is generated in response to mechanical stimuli such as friction, force, pressure, and torque, and various organic or inorganic materials such as SrAl2O4: Eu, Dy (SAO), ZnS: Cu and ZnS: Mn It may be one of fine particles. This light emission phenomenon will be referred to as'mykeno light emission' (ML) hereinafter. Here, the myceno-luminescence phenomenon is also called fracto-, piezo- or elasticoluminescence.

For reference, the Mykeno-luminescent (ML) material adopted in the experiment described in this description is ZnS: Cu (LONCO Company Limited) ML powder among the above materials, and the flexible resin material is polydimethyl siloxane (PDMS).

<Modeling analysis of the correlation between the internal pressure of the eyeball and the behavior of the cornea (C)>

In order to measure intraocular pressure using the Myceno-luminescence (ML) phenomenon, fluid-structure interaction analysis (FSI) is required to analyze the correlation between the internal pressure of the eyeball and the behavior of the cornea (C). . To this end, 3D modeling of a spherical shell (G1) filled with a fluid (mineral oil) was performed during the experiment of the present invention, and FSI analysis was performed through ABAQUS, a commercial finite element method (FEM) analysis tool. The internal pressure and corneal (C) strain were analyzed by applying impulse pressure to the cornea (C). An experiment using a spherical shell (G1) pressurized with a fluid (mineral oil) shows the method for measuring the internal pressure proposed in this study.

In the simplified human eye finite element (FE) model for the preliminary study of internal pressure monitoring, a spherical shell (G1) corresponding to the cornea (C) and sclera (D) was first established as shown in Fig. 2A. Here, in order to increase the efficiency of the analysis and to confirm the operation of the internal components of the eye, in this spherical shell (G1) model, the ocular structure is assumed to be axially symmetric, and the spherical shell (G1) is assumed to have a constant thickness and a constant curvature. The spherical shell G1 was assumed to be filled with a viscous pressurized fluid H1 representing the vitreous body fluid shown in FIG. 2B.

At this time, for the viscoelastic analysis of the viscous pressurized fluid H1 shown in FIG. 2B, a Prony series represented by the following equation was used.

In the above equation, Poisson's ratio υ(t) is assumed to be a constant, τ is the relaxation time, G ₀ is the initial shear modulus, and G _{∞ is the} infinite shear modulus.

The spherical shell (G1) model and the viscous pressurized fluid (H1) model were designed with Lagrangian components. The interaction between two solid elements was defined using the bond constraints between surfaces. The outer diameter and thickness of the spherical shell G1 were arbitrarily set to 65 mm and 2 mm, respectively. The physical properties based on the isotropy of each element are summarized in Table 1 in FIG. 10. ABAQUS, a commercial finite element code, was used in all calculations in this study. Mode-based steady-state dynamic analysis was used to calculate the steady-state dynamic linearized response of the system to harmonic excitation (i.e., steady-state amplitude and phase in complex form).

For the simulation of the non-contact intraocular pressure test, the air puff corresponding to the deformation generating unit prepared to cause the deformation of the Mykeno luminous film 10 has a maximum pressure of 330 kPa, a duration of 40 ms, and a measured collimated air pulse. Was assumed. A circle having a diameter of 3 mm is displayed on the cornea (C) as shown in FIG. 2C.

2D shows a cross section of the spherical shell G1 when the strain of the tip portion of the spherical shell G1 is maximum at various pressures. 2d (a) and (b) show the cross section of the spherical shell G1 at the lowest pressure of 7 kPa, and (c) and (d) show the cross section of the spherical shell G1 at the highest pressure of 27 kPa. Show. 2d (a) and (c) are cross-sections of the spherical shell (G1) when the spherical shell (G1) is deformed by applying time pressure, and (b) and (d) are when the spherical shell (G1) is restored. It is a cross section of the spherical shell G1.

Here, when deformation occurs at each pressure value, in all cases the maximum value of the strain appears twice for various internal pressures. These two peaks are represented in the graph of FIG. 5, and in the graph of FIG. 6, two peaks in which the upper and lower values of I appear at any one pressure value are represented in the symbol marked I in the graph of FIG. 6. These two peaks mean the strain when the spherical shell G1 is deformed by the incident time pressure and is restored by the elasticity of the spherical shell G1.

Here, the strain rate of the Mykeno light-emitting film 10 is the photometric sensor 23. Here, the photometric sensor 23 is a typical photomultiplier tube sensor (PMT). However, any sensor that can measure the intensity of visible light can be adopted.

Intraocular pressure measurement evaluation is performed by the aforementioned fluid-structure interaction analysis (FSI).

The spherical shell (G1) pressurized at 7.5, 10, 12.5, 15 and 17.5 kPa is excited by a vibrator. The experimental results are shown graphically in FIG. 5. Here, the maximum strain appears twice and the emission peak is observed twice at each pressure. This is the light emitted during the transformation and the light emitted during the recovery process. An optical signature is proposed in this study to find the relationship between the characteristics of the emitted light and the internal pressure. This is the ratio of the area expressed as the product of the intensity and duration of the ML. This optical signature can be expressed by the equation below.

Subscripts 1 and 2 of the area represent the first luminescence (eg, the modification process) and the second luminescence (eg, the recovery process) of ML, respectively.

There is a linear relationship between the internal pressure and the optical signature. As shown in the graphs of FIGS. 6A and 6B, a linear relationship is established between the internal pressure and the optical signature. In the above formula, subscripts 1 and 2 of the intensity and area represent the first light emission (eg, the modification process) and the second light emission (eg, the recovery process) of the Mykeno light emission, respectively.

In FIG. 6, a blue symbol I indicates a range of a maximum value and a minimum value. Each pressure and red solid line is a regression line for each optical signature.

<An embodiment of the device for measuring intraocular pressure according to the present invention>

Hereinafter, an embodiment of an apparatus for measuring intraocular pressure according to the present invention will be described with reference to FIGS. 4 and 7 to 9.

As briefly described above, the intraocular pressure measuring device according to the present invention is composed of a deformable film, a deformable generation unit, and a measurement sensor, as shown in FIG. 4, wherein the deformable film is directly on the Mykeno light-emitting film 10. Correspondingly, the measurement sensor is a photometric sensor 23 that accurately measures the intensity of visible light by receiving and amplifying minute visible light emitted when the Mykeno light-emitting film 10 is deformed. At this time, as the photometric sensor 23, a photomultiplier tube sensor (PMT) is representative, but other conventional sensors capable of measuring photometric intensity may also be adopted.

In addition, as shown in FIG. 4, the deformation generating unit generating deformation in the Mykeno light emitting film 10 includes a micro air blower 24 that blows air on the surface of the Mykeno light emitting film 10 to generate pressure in a non-contact manner. Is installed. In this case, an air compressor 242 may be installed in the micro air blower 24. However, any conventional unit can be adopted as long as it can cause minute deformation.

For reference, in the viscous fluid model H2 inside the cornea model G2 shown in FIG. 4, the injection pump S as shown in FIG. 4 may be used to make the internal pressure the same as the inside of the eyeball. .

The photometric sensor 23 shown in FIG. 4 may be measured by holding it by hand, but may be configured to be mounted on a face. To this end, in this embodiment, a frame 30 manufactured to be mounted on a curved face is provided.

Specifically, as shown in FIG. 7, the frame 30 may be mounted using an ear and a nose like ordinary glasses. Since the measurement does not have to be made in both eyes at the same time, the photometric sensor 23 is installed only in one eye, but the photometric sensor 23 installed in one eye area can be pulled out and replaced in the other eye area.

The Mykeno light-emitting film 10 may be brought into contact with the eyeball with a human hand, but since it may be difficult to attach it by hand, in this embodiment, any additional physical contact other than the Mykeno light-emitting film 10 is not applied to the eyeball. As shown in Fig. 8, the Mykeno light-emitting film 10 is held in a spherical shape and held in a spherical shape, and the loading jig 21 installed on the frame 30 so that it can contact the eyeball by moving forward or backward in a sliding method. The light-emitting film 10 is installed. At this time, the curvature forming the spherical shape of the Mykeno light-emitting film 10 coincides with the curvature of the eyeball.

In addition, the loading jig 21 is connected to the circumference of the Mykeno light-emitting film 10 or both sides of the Mykeno light-emitting film 10, and is an elastic support member 22 having a greater elasticity than the Mykeno light-emitting film 10. The light emitting film 10 is held.

That is, when the loading jig 21 grips the Mykeno light-emitting film 10, the rigid member does not directly grip the Mykeno light-emitting film 10, but the flexible elastic support member 22 is shown in FIGS. 8 and 9. As described above, the Mykeno light-emitting film 10 is held. Therefore, the installation of the Mykeno light-emitting film 10 can be made without being disturbed because a solid object comes into contact with the eyeball while the Mykeno light-emitting film 10 is in contact with the eyeball.

A process in which the Mykeno light-emitting film 10 is gently seated on the eyeball due to the elastic support member 22 is illustrated in FIG. 9. At this time, a jig sliding wheel 261 for varying the loading jig 21 in a sliding manner may be installed in the measurement module 20 so that the loading jig 21 can be slowly approached in the eyeball direction, as shown in FIG. 8. have.

In addition, since each person has a different facial skeleton, the distance between the photometric sensor 23 and the eyeball may vary, which may cause an error. To prevent this, the photometric sensor 23 can adjust the distance between the photometric sensor 23 and the eyeball. A sensor sliding wheel 262 that changes) may be installed. Here, a distance measurement sensor (not shown) is additionally installed to generate a signal when the distance between the photometric sensor 23 and the eyeball surface falls within a standard range.

In the control unit 25, a power supply and a communication unit are built-in, and a circuit for receiving signals from each sensor is built-in, so that the measured light intensity data can be exchanged between a smart phone or a server.

On the other hand, the eye line fixation guide module 40 may be installed on the frame 30 in the rest of the eyes other than the eye on the side where the measurement module 20 is installed. In particular, the gaze fixing induction module 40 prevents the phenomenon that the Mykeno light-emitting film 10 cannot be seated in the correct position due to the complicated movement of the eyeball due to the eye protection during the installation process of the Mykeno light-emitting film 10. It acts to generate a visual signal for focusing the gaze that can fix the gaze for the purpose.

In addition, the eyepiece sealing member 31 for sealing the measurement module 20 and the skin around the eye is provided to block ambient light, so that the light intensity measurement can be made more precisely.

The present invention described above is not limited by the above-described embodiments and the accompanying drawings, and various substitutions, modifications and changes are possible within the scope of the technical spirit of the present invention. It will be obvious to those who have the knowledge of.

A: lens B: iris
C: cornea D: sclera
E: optic nerve F: vitreous body fluid
G1: spherical shell G2: corneal model
H1: viscous pressurized fluid H2: viscous fluid model
L: Visible light emitted P: Force applied for deformation
S: Injection pump 10: Mykeno luminescent film
20: measurement module 21: loading jig
22: elastic support member 23: photometric sensor
24: micro air blower 25: control unit
30: frame 31: eyepiece sealing member
40: gaze fixed induction module 242: air compressor
261: jig sliding wheel 262: sensor sliding wheel
263: power switch 264: measurement start switch

Claims (7)

A deformable film made of a flexible material;
A deformation generating unit for applying a force to the deformable film so that deformation occurs in the deformable film;
Consisting of a measurement sensor that detects the degree of deformation generated in the deformation film due to the deformation generation unit,
The deformable film is a composite material in which a photomechanical light-emitting material and a flexible resin material that emit light when mechanical deformation is applied are mixed with each other, and is manufactured in the form of a thin film that can be attached to the eye, so that light emission is generated in response to the mechanical change of the surface. Intraocular pressure measuring device which is the induced Mykeno luminescent film 10. The method of claim 1,
The mykeno light-emitting film 10 is an intraocular pressure measuring device, characterized in that formed in a curved surface having the same curvature as the outer surface of the eyeball. The method of claim 1,
The deformation generating unit is a micro-air blower (24), characterized in that the micro-air blower (24) for applying a micro-deformation to the surface of the Mykeno light-emitting film (10) by blowing air to the surface of the Mykeno light-emitting film (10). The method of claim 1,
The measurement sensor for detecting the degree of deformation is a photometric sensor 23 that receives and amplifies microscopic visible light generated by microscopic deformation of the surface of the Mykeno light-emitting film 10 to measure the intensity of visible light. Intraocular pressure measuring device. The method of claim 4,
The Mykeno light-emitting film 10, the deformation generating unit, and the photometric sensor 23 are installed in a frame 30 manufactured to be mounted on a curved face. The method of claim 5,
The Mykeno light-emitting film 10 is attached to the loading jig 21 installed on the frame 30 so that the Mykeno light-emitting film 10 is held in a spherical shape and is held in a sliding manner, so that it can be brought into contact with the eyeball by moving forward or backward in a sliding manner. An intraocular pressure measuring device, characterized in that it is installed. The method of claim 6,
The loading jig 21 is connected to the circumference of the Mykeno light-emitting film 10 or both sides of the Mykeno light-emitting film 10, and is an elastic support member 22 having a greater elasticity than the Mykeno light-emitting film 10. An apparatus for measuring intraocular pressure, characterized in that gripping the luminescent film 10.

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