KR102293313B1 - Non-contact type tonometer - Google Patents

Abstract

The non-contact intraocular pressure measuring device includes a housing, an air generating unit generating compressed air, a nozzle unit spraying the air generated by the air generating unit, a sensor unit disposed in front of the nozzle unit, and the IOP based on values measured by the sensor unit It includes an arithmetic unit for calculating .

Description

Non-contact tonometer {NON-CONTACT TYPE TONOMETER}

The present invention relates to a non-contact tonometer, and more particularly, to a non-contact tonometer capable of facilitating the measurement of intraocular pressure by a measurer.

Intraocular pressure (IOP) is the pressure applied to the eyeball by the aqueous humor, which is a solution that fills between the cornea and the lens of the eyeball. The normal intraocular pressure is generally about 10 mmHg to 21 mmHg, and the normal intraocular pressure plays a role in maintaining the shape and function of the eyeball.

However, when an abnormality occurs in the production and discharge of aqueous humor and an abnormal level of intraocular pressure occurs, the fibrous layer of the retinal optic nerve may be damaged or a serious disease such as glaucoma may be caused, resulting in loss of vision. Therefore, accurate intraocular pressure measurement is very important for early detection and treatment of ophthalmic diseases.

An intraocular pressure measuring device for measuring intraocular pressure may be classified into a contact type and a non-contact type depending on whether a part of the device and the cornea are in direct contact.

A representative contact-type intraocular pressure measurement device is the Goldmann Applanation Tonometer (GAT), which works when the cornea reaches a flattened state (applanation) after pressing the center of the cornea with a probe with a built-in prism. measure the force The Goldman applanation tonometer has a clear measurement principle and is used as a standard device to evaluate the accuracy of intraocular pressure values measured by other methods. However, corneal anesthesia is required to measure intraocular pressure, there is a risk of infection due to this, and part of the device must be kept in contact with the eye during the examination, which may cause fear and discomfort to the examinee. In addition, there is a disadvantage that the operation of an experienced ophthalmologist is required for accurate measurement.

A representative contactless typed tonometer (NCT) injects compressed air into the cornea by driving a solenoid, flattens the cornea with air pressure, and uses a complex image sensing and analysis device to check whether flattening or not. The intraocular pressure is calculated from the time required for appraisal and the applied air pressure. The non-contact intraocular pressure measuring device does not require eye drop anesthesia, and since the test is performed instantaneously, inconvenience to the examinee can be minimized.

Such a non-contact intraocular pressure measuring device has the advantage of being able to measure itself. However, in order to measure intraocular pressure by oneself without the help of a specialist, it is necessary to align the tonometry at the center of the eye to be measured and to position the tonometry at the measuring distance that can be measured. It is difficult to measure

Korean Patent Application Laid-Open No. 10-2017-0002182 (2017.01.06)

Accordingly, it is an object of the present invention to provide a non-contact tonometer capable of easily and accurately self-measurement of intraocular pressure by facilitating alignment of the tonometer for accurate measurement.

The non-contact intraocular pressure measuring device according to an embodiment for realizing the object of the present invention is disposed on the front of the housing, the air generating unit for generating compressed air, the nozzle unit for spraying the air generated by the air generating unit, and the nozzle unit It includes a sensor unit and a calculation unit for calculating intraocular pressure based on the value measured by the sensor unit.

In one embodiment of the present invention, the nozzle unit is connected to the air generating unit and an air supply unit having at least two branched air passages, a nozzle tip having one end connected to the inside of the air supply unit and the other end tapering toward the center; It may include a nozzle cap having one end connected to the outside of the air supply unit and the other end tapering toward the center. The air supply unit may include a plurality of pneumatic inlets that are outlets of the air passages communicating with the first and second extended passages of the air passages.

In an embodiment of the present invention, the sensor unit is disposed on the front surface of the nozzle unit, the first light emitting unit emitting infrared light and the first light emitting unit and the first light emitting unit are disposed adjacent to each other in a first direction perpendicular to the ground, A center sensor including a first light receiving unit for accommodating it, a second light emitting unit which is disposed adjacent to the center sensor in a second direction perpendicular to the first direction, and a second light emitting unit and the second light emitting unit to emit infrared light in the first direction a first left and right sensor including a second light receiving unit for accommodating infrared rays, and a first left and right sensor disposed in a position symmetrical to the first central alignment sensor in the second direction with respect to the center sensor, and emitting infrared rays and a third light emitting unit and a second left and right sensor disposed adjacent to the third light emitting unit in the first direction and including a third light receiving unit for accommodating infrared rays.

In an embodiment of the present invention, the center sensor senses the distance between the center sensor and the eye to be measured, and an alignment guide unit for guiding at least one of center alignment and measuring the distance between the center sensor and the eye to be measured. Further comprising, the alignment guide portion is disposed inside the guide hole and the nozzle tip formed in the shape of a hole penetrating the nozzle tip to have a predetermined angle inclination, different colors depending on the distance between the center sensor and the eye to be measured It may include a guide light-emitting unit that emits light.

In an embodiment of the present invention, the guide light emitting unit may emit blue light when the distance between the center sensor and the eyeball to be measured is 6.5 mm or more, green when the distance between 5.5 mm or more and less than 6.5 mm, and red when the distance between the center sensor and the eye to be measured is less than 5.5 mm.

In an embodiment of the present invention, the calculating unit compares the voltage value received in the second light receiving unit with the voltage value received in the third light receiving unit, and the voltage value received in the second light receiving unit and the third light receiving unit When the difference between the accepted voltage values is 10 mV or less, the intraocular pressure may be calculated based on the value measured by the central sensor.

In one embodiment of the present invention, the operation unit injects air into the eye from the nozzle unit, and the voltage value accommodated by the first light receiving unit increases from the first voltage value and then returns to the first voltage value again. Time is measured, and the intraocular pressure can be calculated according to the deformation recovery time.

In an embodiment of the present invention, the calculating unit may calculate the intraocular pressure by measuring a voltage value accommodated by the first light receiving unit at a specific time.

According to embodiments of the present invention, the non-contact IOP includes the first and second left and right sensors to facilitate left and right alignment when measuring intraocular pressure, and the alignment guide guides an appropriate distance for measurement, enabling measurement of intraocular pressure at an appropriate distance do. Therefore, self-measurement of intraocular pressure is easy.

1 is a side view illustrating a non-contact intraocular pressure meter according to an embodiment of the present invention.
2 is a block diagram illustrating a non-contact intraocular pressure meter according to an embodiment of the present invention.
3 is an exploded perspective view illustrating a non-contact intraocular pressure meter according to an embodiment of the present invention.
4 is a side view illustrating a nozzle unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.
5 is a front view illustrating a nozzle unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.
6 is a cross-sectional view illustrating an alignment guide part of a non-contact IOP measurement device according to an embodiment of the present invention.
7 is a perspective view illustrating an air supply unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.
8 is a perspective view illustrating an air supply unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.
9 is an internal structural diagram illustrating an air supply unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.
10 is an exploded perspective view illustrating a nozzle tip and a sensor unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.

Since the present invention may have various changes and may have various forms, embodiments will be described in detail in the text. However, this is not intended to limit the present invention to the specific disclosed form, it should be understood to include all modifications, equivalents and substitutes included in the spirit and scope of the present invention. In describing each figure, like reference numerals have been used for like elements. Terms such as first, second, etc. may be used to describe various elements, but the elements should not be limited by the terms.

The above terms are used only for the purpose of distinguishing one component from another. The terms used in the present application are only used to describe specific embodiments, and are not intended to limit the present invention. The singular expression includes the plural expression unless the context clearly dictates otherwise.

In the present application, terms such as "comprises" or "consisting of" are intended to designate that a feature, number, step, operation, component, part, or combination thereof described in the specification is present, but one or more other features It is to be understood that it does not preclude the possibility of the presence or addition of numbers, steps, operations, components, parts, or combinations thereof.

Unless defined otherwise, all terms used herein, including technical and scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Terms such as those defined in commonly used dictionaries should be interpreted as having a meaning consistent with the meaning in the context of the related art, and should not be interpreted in an ideal or excessively formal meaning unless explicitly defined in the present application. does not

Hereinafter, preferred embodiments of the present invention will be described in more detail with reference to the drawings.

1 is a side view illustrating a non-contact intraocular pressure meter according to an embodiment of the present invention. 2 is a block diagram illustrating a non-contact intraocular pressure meter according to an embodiment of the present invention. 3 is an exploded perspective view illustrating a non-contact intraocular pressure meter according to an embodiment of the present invention. 4 is a side view illustrating a nozzle unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention. 5 is a front view illustrating a nozzle unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.

1 to 5 , the non-contact intraocular pressure measuring device according to an embodiment of the present invention includes an air generating unit 110 that generates compressed air, a display unit that controls the compressed air supply and measures intraocular pressure and displays the measurement result. It may include an electric length unit 130 including a, and a nozzle unit 150 for spraying the air generated by the air generating unit 110 .

Here, the housing 100 is a main case, a sub-case corresponding to and engaged with the main case, a transparent window 105 mounted on one side of the main case to display an LCD, and the window 105 is disposed around and At least one switch 107 including a power switch for supplying power through a battery (not shown) mounted inside the housing 100, a mode switch for displaying a mode, a selection switch for selecting a mode, etc. may include.

In addition, the housing 100 may have a portable size and shape, and for convenience when measuring intraocular pressure, at least one side of the housing 100 may protrude at least partially or a hole may be formed. Accordingly, the measurer can easily hold the housing 100 by hand.

The air generating unit 110 includes an air pump 111 for compressing air, an air filter 113 connected to the air pump 111 and filtering the compressed air flowing in from the air pump 111 , the air An air tank 115 that is connected to the filter 113 and stores compressed air filtered through the air filter 113, is connected to the air tank 115 and blows the compressed air stored in the air tank 115, or It may include an injection valve 117 that opens and closes to block and controls the supply of air, and a mounting bracket 119 for collectively mounting the air tank 115 and the injection valve 117 .

In addition, the air generating unit 110 is connected to the air tank 115 and measures whether the pressure of the compressed air stored in the air tank 115 reaches a preset pressure to operate the air pump 111 . It may include a pressure sensor (not shown) for the air tank to stop the.

The electric unit 130 includes a PCB assembly mounted on the air tank 115, a backlight connected to the PCB assembly and mounted on the PCB assembly, and an LCD connected to the backlight and mounted on the backlight to emit light. may include

The calculation unit 140 may calculate the intraocular pressure based on the value measured by the sensor unit 160 . A method in which the calculating unit 140 calculates the intraocular pressure based on the value measured by the sensor unit 160 will be described later.

The nozzle unit 150 includes an air supply unit 151 , a nozzle tip 157 having one end connected to the inside of the air supply unit 151 , the other end tapering toward the center, and mounted on the front end of the air supply unit 151 , and the air A nozzle cap 159 having one end connected to the outside of the supply unit 151 and the other end tapering toward the center may include a nozzle cap 159 into which the nozzle tip 157 is inserted. A ring type inclined by the space created between the other inclined end of the nozzle tip 157 inserted into the nozzle cap 159 and the other inclined end of the nozzle cap 159 into which the other inclined end of the nozzle tip 157 is inserted. A flow path 153 may be formed.

The front surface of the nozzle tip 157 may include a circular protrusion 158 having both sides convex outward in the first direction D1 direction perpendicular to the ground centering on the center sensor 161 . The circular protrusion 158 precisely maintains a certain distance between the inner and outer surfaces of the inclined ring-shaped flow path 153, so that air passing through the ring-shaped flow path 153 and injected into the cornea can be uniformly ejected. .

The sensor unit 160 may be disposed in front of the nozzle unit 150 . The sensor unit 160 may include a center sensor 161 , a first left and right sensor 162 , and a second left and right sensor 163 .

The center sensor 161 is disposed adjacent to the first light emitting part 161a and the first light emitting part 161a emitting infrared rays within a predetermined distance in a first direction D1 perpendicular to the ground, and receiving infrared rays. and a first light receiving unit 161b.

The first left and right sensors 162 are separated from the center sensor 161 at a predetermined distance in a second direction D2 perpendicular to the first direction D1 (a first light emitting unit 161a and a first light receiving unit within the center sensor). (which may be different from a certain distance in 161b)) may be disposed adjacent to each other. The first left and right sensors 162 are located within a predetermined distance from the second light emitting unit 162a and the second light emitting unit 162a emitting infrared light in the first direction D1 (the first light emitting unit in the center sensor) 161a) and a predetermined distance from the first light receiving unit 161b) are disposed adjacent to each other, and may include a second light receiving unit 162b for accommodating infrared rays.

The second left and right sensors 163 may be disposed at a position symmetrical to the first center alignment sensor 161 in the second direction D2 . The second left and right sensors 163 are located within a predetermined distance from the third light emitting unit 163a and the third light emitting unit 163a emitting infrared light in the first direction D1 (the first light emitting unit (in the center sensor) 161a) and a predetermined distance from the first light receiving unit 161b) are disposed adjacent to each other, and may include a third light receiving unit 163b for accommodating infrared rays.

The alignment guide unit 170 may guide center alignment (center alignment means that the center of the nozzle unit and the center of the target's eyeball coincide within a certain error range). The alignment guide unit 170 is disposed inside the guide hole 171 and the nozzle tip formed in the shape of a hole penetrating the nozzle tip so as to have a predetermined inclination, and between the center sensor 161 and the eye to be measured. It may include a guide light emitting unit 173 that emits different colors according to the distance of . In addition, the guide light emitting unit 173 may display a center alignment mark, and when the center alignment is within a predetermined error range (the predetermined error is determined by the target accuracy), the guide hole 171 is The center alignment mark shown through may be placed in the center of the guide hole 171 to be seen. The center alignment mark may be formed as a circular point or a mark having various shapes.

The calculating unit compares the voltage value received by the second light receiving unit 162b with the voltage value received by the third light receiving unit 163b, and the voltage value received by the second light receiving unit 162b and the third light receiving unit ( When the difference between the voltage values accommodated in 163b) is less than or equal to a predetermined threshold, the intraocular pressure may be calculated based on the value measured by the central sensor. For example, the predetermined threshold may be 10 mV.

That is, when the difference between the voltage value received by the second light receiving unit 162b and the voltage value received by the third light receiving unit 163b is less than or equal to a predetermined threshold, it means that the left and right directions are aligned, which is Since the left and right sides of the nozzle match the center of the nozzle within a certain error range, the alignment in the left and right directions is judged to be at a level that is not unreasonable for measuring intraocular pressure, and intraocular pressure is measured. The second light receiving unit 162b and the third light receiving unit 163b receive infrared rays reflected from the eyeball, and when the nozzle unit center and the eyeball center are placed so that they coincide within a predetermined error range, the second light receiving unit 162b and The voltage value accommodated by the third light receiving unit 163b has a value within the error range. Accordingly, when the difference between the voltage values received by the second light receiving unit 162b and the third light receiving unit 163b is less than or equal to a predetermined threshold, it may be determined that the center of the nozzle unit 150 and the center of the eyeball are aligned.

For example, when the difference between the voltage value received by the second light receiving unit 162b and the voltage value received by the third light receiving unit 163b is 10 mV or less, it is determined that the left and right alignment is appropriate and the intraocular pressure is measured. and, if the difference between the voltage value received by the second light receiving unit 162b and the voltage value received by the third light receiving unit 163b is greater than 10 mV and less than 20 mV, at this time, it may be suspected that the left and right alignment is not correct. can Accordingly, it may be determined that the intraocular pressure is not measured at this time, or that the measured intraocular pressure value is unreliable. In addition, when the difference between the voltage value received by the second light receiving unit 162b and the voltage value received by the third light receiving unit 163b exceeds 20 mV, it is displayed as a measurement error, and the measured intraocular pressure value can be ignored. . However, the present invention is not limited thereto, and the predetermined threshold may be appropriately changed according to a measurement environment and a target implementation accuracy.

Also, the center sensor 161 may measure the distance between the nozzle unit and the center of the eyeball. That is, the infrared ray from the first light emitting unit 161a of the center sensor 161 is reflected from the eyeball and then measured by the first light receiving unit 161b to measure the distance between the nozzle unit and the center of the eyeball. Alternatively, the distance between the nozzle unit and the center of the eyeball may be measured by using not only the center sensor 161 but also the first left and right sensors 162 and the second left and right sensors 163 to further increase measurement accuracy. In this case, the distance can be measured by calculating the measured values in consideration of the arrangement positions of the three sensors (that is, the center sensor 161 measures the distance to the front of the eyeball, and the first left and right sensors 162 and the second left and right sensors) Since the sensor 162 measures the distance to the side of the eyeball, the distance is measured in consideration of this positional relationship).

On the other hand, the calculation unit is the center of the cornea of the eyeball is deformed due to the voltage value received by the second light receiving unit 162b, the voltage value received by the third light receiving unit 163b, and the air injected from the air generating unit 110 . The intraocular pressure may be derived using the voltage value at the time of light reception of the infrared light emitted by the sensor 161 .

For example, when the cornea of the eye is flattened, the voltage received by the second light receiving unit 162b and the third light receiving unit 163b may be a specific voltage value (for example, it may be a maximum voltage value). The intraocular pressure may be derived by using the voltage value at the time of light reception of the infrared light emitted by the central sensor 161 .

6 is a cross-sectional view illustrating an alignment guide part of a non-contact IOP measurement device according to an embodiment of the present invention.

Referring to FIG. 6 , the alignment guide unit 170 of the non-contact tonotonometer according to an embodiment of the present invention may include a guide hole 171 and a guide light emitting unit 173 .

The guide hole 171 may be formed in the shape of a hole passing through the nozzle tip 157 to have a predetermined angle (A) inclination. For example, the angle A formed by the guide hole 171 with the ground may be 5.5 degrees or more and 6.5 degrees or less, and preferably 6 degrees.

The guide light emitting part 173 is disposed inside the nozzle tip 157 and may emit different colors according to the distance between the center sensor 161 and the eye to be measured. The guide light emitting part 173 may be located in a direction inclined at a predetermined angle (A) from the eyeball. The guide light emitting part 173 may emit different colors according to the distance from the eyeball measured by the center sensor 161 . For example, the guide light emitting unit 173 is green when the distance between the center sensor 161 and the eye to be measured is greater than or equal to the first distance and less than the second distance, blue when the second distance or more, and red when the distance between the center sensor 161 and the eye to be measured is less than the first distance. can emit light. For example, blue light may be emitted when the diameter is greater than or equal to 6.5 mm, green light can be emitted when the diameter is greater than or equal to 5.5 mm and less than 6.5 mm, and red light can be emitted when the diameter is less than 5.5 mm.

In addition, a light emitting lamp (not shown) emitting different colors according to the distance from the eyeball measured by the center sensor 161 may be configured to be disposed inside the nozzle cap 159 . The light emitting lamp may be an LED, and when the distance between the center sensor 161 and the eyeball to be measured is less than the first distance or more and less than the second distance, green light is emitted, blue when the second distance or more, and red light is emitted when the distance is less than the first distance. can The light emitting lamp is disposed inside the nozzle cap 159 so that the user can check the color emitted through the ring-shaped flow path 153 .

Alternatively, as described above, the distance is measured by using not only the center sensor 161 but also the first left and right sensors 162 and the second left and right sensors 163 at the same time, and depending on the distance measured therefrom, a light emitting lamp or a guide light emitting unit 173 ) can be controlled.

Accordingly, when the green light is emitted, the user determines that the intraocular pressure measurement distance is set appropriately and can measure the intraocular pressure at this time, thereby making it easy to self-measure the intraocular pressure.

7 is a perspective view illustrating an air supply unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention. 8 is a perspective view illustrating an air supply unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention. 9 is an internal structural diagram illustrating an air supply unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention. 10 is an exploded perspective view illustrating a nozzle tip and a sensor unit of a non-contact intraocular pressure measurement device according to an embodiment of the present invention.

Referring to FIGS. 3 and 7 to 10 , the air supply unit 151 of the non-contact intraocular pressure gauge according to an embodiment of the present invention is an air tank 115 by opening the injection valve 117 of the electric unit 130 . It may include an air passage 152 branched into at least two from which compressed air is ejected. Here, the injection valve 117 may be a solenoid valve, and may be operated by at least one or more switches 107 .

The air passage 152 is a first branch passage including a connection passage 152-1 connected to the injection valve 117 and a first branch 152-2 branching from the connection passage 152-1. 152 - 4 and a first extension passage portion 152 - 6 extending from the first branch passage 152 - 4 and substantially parallel to the connection passage 152-1 .

In addition, the air flow path 152 is a connection flow path 152-1 connected to the injection valve 117, and a second branch branching in a different direction from the first branch part 152-2 in the connection flow path 152-1. A second branch passage 152 - 5 having a second branch 152 - 3 and a second extension passage extending from the second branch passage 152 - 5 and substantially parallel to the connection passage 152-1 . part 152 - 7 may be included.

Also, the first branch flow path 152-4 has a smaller cross-sectional area as it goes from the first branch part 152-2 to the first extension flow path part 152-6, and the second branch flow path 152-5 has a smaller cross-sectional area. has a smaller cross-sectional area from the second branch portion 152 - 3 to the second extension passage portion 152 - 7 . Due to this configuration, the air flowing through the first branch passage 152 - 4 and the second branch passage 152 - 5 respectively flows from the first branch portion 152 - 2 to the first extension passage portion 152 - 6 . The flow of air becomes faster as it goes from the second branching part 152-3 to the second extension flow passage part 152-7, and the air pressure is sprayed to the cornea spaced apart by a predetermined distance through a small nozzle to effectively make the cornea. can be transformed.

The first extension passage 152 - 6 and the second extension passage 152 - 7 may be connected to the ring-shaped passage 153 .

The nozzle tip 157 may be separated and coupled to upper and lower portions 157a and 157b, and the front surface of the combined nozzle tip 157 may have a recessed groove shape toward the center.

The air supply unit 151 includes a plurality of pneumatic inlets 155 communicating with the first and second extended passages 152 - 6 and 152 - 7 of the air passage 152 . Air may flow out into the nozzle cap 159 mounted on the outside of one end of the air supply unit 151 through the 155 . Here, the pneumatic inlet 155 is the outlet of the air flow path 152 .

The other end of the nozzle tip 157 to which one end of which the protrusion 154b is mounted is inserted into the groove 154a formed on the inner side of the air supply unit 151 is tapered inward, that is, toward the center of the nozzle tip 157. The other end of the nozzle cap 159 has a shape, and the other end of the nozzle cap 159, which has one end fitted with a protrusion and is connected to the groove formed on the outside of the air supply unit 151, also has a tapered shape inward, that is, toward the center of the nozzle cap 159. .

Accordingly, the nozzle tip 157 and the nozzle cap 159 form a ring-shaped flow path 153 connected to the air flow path 152 . Here, the radius of the inwardly tapered nozzle tip 157 is smaller than the radius of the inwardly tapered nozzle cap 159 . In other words, the radius of the ring-shaped passage 153 corresponds to a value obtained by subtracting the radius of the inwardly tapered nozzle tip 157 from the radius of the inwardly tapered nozzle cap 159, and the end of the ring-shaped passage 153 is is the nozzle Here, the nozzle tip 157 and the nozzle cap 159 may have the same or different tapered inclinations. Thus, the inclined space has a constant inclination or a different inclination.

The non-contact intraocular pressure meter according to an embodiment of the present invention is a non-contact intraocular pressure meter that facilitates self-measurement. First, the user arranges the intraocular pressure meter at a position where accurate measurement is possible, and when it is confirmed that it is placed at a position where accurate measurement is possible, the intraocular pressure is measured. carry out

That is, the distance between the center sensor 161 of the center of the eyeball and the center of the nozzle is maintained within an appropriate distance for a predetermined time (the first left and right sensors 162 and the second left and right sensors 163 may also be used for distance measurement). When the left and right alignment is within a certain error range through the measurement values from the left and right sensors 162 and the second left and right sensors 163, the light emitting lamp (or the guide light emitting unit 173) emits light in a first color (eg, green), , the user gazes at the alignment mark through the guide hole.If this state is maintained for a certain period of time, it is determined that alignment is achieved, and air is injected through the ring-shaped flow path 153. At the same time as the air is injected, the center sensor 161 ), the central sensor 161 measures the infrared emission from the center sensor 161 and measures the degree of deformation of the eyeball according to the amount of injected air to calculate the intraocular pressure (as described above, the first left and right sensors 162 and the second left and right sensors) 163 also emits infrared rays to the eyeball when air is sprayed, and receives the reflected light reflected from the eyeball to be used for intraocular pressure calculation. In this case, the first left and right sensors ( 162) and/or the degree of light received by the second left and right sensors 163 and the degree of light received by the first left and right sensors 162 and/or the second left and right sensors 163 with respect to the infrared light emitted by the second left and right sensors 163 can be used).

On the other hand, if a safe distance is secured between the nozzle center and the eye area, air is sprayed from the nozzle part to the center of the eyeball within a certain period of time. By measuring the amount of infrared rays received by the left and right sensors 162 and 163 and/or the central sensor 161 by emitting , it is determined whether the cornea of the eye is flattened from these measurements, and the intraocular pressure can be calculated using these received infrared measurements. . Alternatively, even if it is not determined whether the cornea of the eye is flattened, the intraocular pressure can be calculated using the received infrared measurement values through infrared light emission from the central sensor 161 and the left and right sensors 162 and 163 and light received by the respective sensors (must be three sensors). measurement is possible without using the center sensor 161 or the first left and right sensors and the second left and right sensors).

On the other hand, the calculating unit of the non-contact intraocular pressure measuring device according to an embodiment of the present invention injects air into the eye from the nozzle unit, and the voltage value accommodated by the first light receiving unit increases from the first voltage value and then back to the first voltage value. The return strain recovery time may be measured, and the intraocular pressure may be calculated according to the strain recovery time.

For example, the time between the second time point (t2) when the signal intensity increases at the first time point (t1) when the signal strength is 1.5 mV and returns to 1.5 mV is calculated, and the intraocular pressure is calculated according to this time. can The time between the first time point (t1) and the second time point (t2), that is, the deformation recovery time is the time the eyeball is deformed by the sprayed air and then returns to its original shape, and has a different value depending on the intraocular pressure. do. Therefore, it is possible to store the data by measuring the deformation recovery time according to the intraocular pressure in advance, and to calculate the intraocular pressure by comparing the stored data and the measured deformation recovery time. When the deformation recovery time does not exactly match, the calculator may calculate the intraocular pressure in proportion to the deformation recovery time.

Meanwhile, the calculating unit of the non-contact intraocular pressure measuring device according to an embodiment of the present invention may calculate the intraocular pressure by measuring the voltage value accommodated by the first light receiving unit at a specific time.

The intraocular pressure can be calculated by measuring the signal strength received by the first light receiving unit at a specific time point (t1, t2, t3, etc.) and comparing it with the signal strength previously measured at a specific time point (t1, t2, t3, etc.) have. The signal strength measured in advance at a specific time point (t1, t2, t3, etc.) according to the intraocular pressure may vary depending on how the specific time point is set. For example, when the intraocular pressure is 5 mmHg, the pre-measured signal strength at the first time point t1 is 3 mV, and when the signal strength measured in advance at the first time point t1 is 3 mV, the measurer's intraocular pressure is calculated as 5 mmHg can do.

Although described above with reference to the embodiments, those skilled in the art can variously modify and change the present invention within the scope without departing from the spirit and scope of the present invention described in the claims below. You will understand that there is

100: housing
110: air generating unit
130: battlefield
140: arithmetic unit
150: nozzle unit
160: sensor unit
170: alignment guide unit

Claims (8)

housing;
Air generating unit for generating compressed air;
a nozzle unit for spraying the air generated by the air generating unit;
a sensor unit disposed in front of the nozzle unit; and
and a calculation unit for calculating intraocular pressure based on the value measured by the sensor unit,
The nozzle unit,
an air supply unit connected to the air generating unit and having at least two branched air passages;
a nozzle tip having one end connected to the inner side of the air supply and the other end tapering toward the center;
and a nozzle cap having one end connected to the outside of the air supply unit and the other end tapering toward the center,
The air supply unit includes a plurality of pneumatic inlets that are outlets of the air passage communicating with the first and second extension passages of the air passage,
The sensor unit is disposed in front of the nozzle unit,
a center sensor including a first light emitting unit emitting infrared light and a first light receiving unit disposed adjacent to the first light emitting unit in a first direction perpendicular to the ground and receiving infrared light;
A second light emitting unit disposed adjacent to the center sensor in a second direction perpendicular to the first direction, a second light emitting unit emitting infrared light, and a second light emitting unit emitting infrared light and disposed adjacent to the second light emitting unit in the first direction, receiving infrared light a first left and right sensor including two light receiving units; and
A third light emitting part symmetrical to the first center alignment sensor in the second direction with respect to the center sensor and a third light emitting part emitting infrared light and the third light emitting part are disposed adjacent to each other in the first direction, A non-contact intraocular pressure measurement device including a second left and right sensor including a third light receiving unit for receiving.
delete delete According to claim 1, wherein the center sensor senses the distance between the center sensor and the eye to be measured,
Further comprising an alignment guide unit for guiding at least one of center alignment and measuring the distance between the center sensor and the eye to be measured,
The alignment guide part,
a guide hole formed in the shape of a hole passing through the nozzle tip to have a predetermined angle of inclination; and
A non-contact tonometer comprising a guide light emitting part disposed inside the nozzle tip and emitting different colors depending on the distance between the center sensor and the eye to be measured.
The method of claim 4, wherein the guide light-emitting unit,
When the distance between the center sensor and the eye to be measured is greater than or equal to the first distance and less than the second distance, a green light is emitted when the distance is greater than or equal to the second distance, blue when the distance is greater than the second distance, and red when the distance between the central sensor and the eye to be measured is less than the first distance.
The method of claim 1, wherein the calculating unit,
comparing the voltage value received in the second light receiving unit with the voltage value received in the third light receiving unit;
When the difference between the voltage value received by the second light receiving unit and the voltage value received by the third light receiving unit is less than or equal to a predetermined threshold, the non-contact intraocular pressure measuring device calculates the intraocular pressure based on the value measured by the central sensor.
The method of claim 1, wherein the operation unit injects air into the eye from the nozzle unit and measures the deformation recovery time in which the voltage value accommodated by the first light receiving unit increases from the first voltage value and then returns to the first voltage value. do,
A non-contact intraocular pressure measuring instrument for calculating intraocular pressure according to the deformation recovery time.
The non-contact intraocular pressure measuring device of claim 1 , wherein the calculating unit calculates the intraocular pressure by measuring the voltage value received by the first light receiving unit at a specific time.

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