Non-contact portable intraocular pressure measurement system and method utilizing infrared intensity differences

Abstract

This invention relates to a non-contact portable intraocular pressure (IOP) measurement system and method utilizing differences in infrared light intensity. A nozzle module receives compressed air from a compressed air supply source and sprays it onto the cornea of ​​a subject through an air jet nozzle to deform the cornea. An infrared sensor is disposed within the nozzle module to measure the amount of light reflected from the cornea by emitting infrared light towards it. A controller is used to convert the amount of light measured by the infrared sensor before and after corneal deformation into IOP.

Description

Technical Field

[0001] This invention relates to an intraocular pressure measurement system capable of early diagnosis and prevention of glaucoma and other conditions. Background Technology

[0002] Glaucoma, along with diabetic retinopathy and macular degeneration, is known as one of the three major causes of blindness. Because there are no specific symptoms from the onset to the end of the disease, more and more patients are diagnosed with end-stage glaucoma when they are diagnosed with the disease.

[0003] The primary cause of glaucoma is elevated intraocular pressure (IOP) when the production of aqueous humor, the fluid filling the anterior chamber between the cornea and iris, is higher than normal, or when obstruction of aqueous humor flow reduces its outflow. Elevated IOP can compress or damage the optic nerve in the retina, ultimately leading to blindness. Therefore, for early diagnosis and prevention of glaucoma, an IOP measurement system that allows patients to regularly measure and manage their own IOP is needed.

[0004] Traditional intraocular pressure (IOP) measurement systems can be categorized into contact and non-contact types. Contact IOP measurement systems are further divided into tonometry and applanation types. Tonometry involves placing a plunger directly in contact with the cornea and measuring the displacement of the plunger's indentation, which is then converted into IOP. Applanation types involve placing a pressure body in contact with the eyeball and converting the force applied to applanate a specified area of ​​the cornea into IOP.

[0005] The biggest problem with contact tonometry systems is that they require anesthesia with eye drops administered by a specialist, and the direct contact of the plunger or pressure body with the cornea can cause corneal damage and infectious eye infections. In contrast, non-contact tonometry systems have the advantages of short measurement time and no need for anesthesia with eye drops, but they have disadvantages such as inaccurate measurements when the corneal surface is irregular, limitations in miniaturization, and high cost. Summary of the Invention

[0006] Technical issues

[0007] The technical problem of the present invention is to provide a non-contact portable intraocular pressure measurement system and method that utilizes the difference in infrared intensity: glaucoma can be diagnosed in advance even in ordinary households, and regular eye examinations and early detection of glaucoma can be performed, thereby minimizing the damage caused by the disease.

[0008] Problem-solving methods

[0009] The present invention, which addresses the aforementioned technical problem, utilizes a non-contact portable intraocular pressure measurement system based on differences in infrared intensity. This system includes a nozzle module, an infrared sensor, and a controller. The nozzle module receives compressed air from a compressed air supply source and ejects it through an air jet nozzle onto the cornea of ​​a subject to deform the cornea. The infrared sensor, disposed within the nozzle module, measures the amount of light reflected from the cornea by emitting infrared light towards it. The controller converts the amount of light measured by the infrared sensor before and after corneal deformation into intraocular pressure.

[0010] The infrared sensor may include: a sensor support block disposed within the nozzle module; a light-emitting device supported by the sensor support block to emit infrared light toward the cornea; and a pair of light-receiving devices disposed on both sides of the light-emitting device and supported by the sensor support block to receive light reflected from the cornea and measure the amount of light.

[0011] Furthermore, the nozzle module may include: a nozzle body, a sensor support block fixed at the center, and an air supply port formed at the edge for receiving compressed air from a compressed air supply source; and a nozzle tip, an air injection port formed at the center and housing the sensor support block together with the nozzle body, receiving compressed air supplied through the air supply port between the nozzle tip and the nozzle body and injecting it through the air injection port.

[0012] Furthermore, a non-contact portable intraocular pressure measurement system utilizing infrared intensity differences may include a pressure sensor disposed within a nozzle module to receive compressed air ejected from the nozzle module and reflected from the cornea to measure air pressure. The controller then converts the air pressure measured by the pressure sensor before and after corneal deformation into intraocular pressure by correlating the amount of light measured by the infrared sensor.

[0013] The intraocular pressure measurement method of the present invention utilizing infrared intensity differences includes: the steps of: ejecting compressed air into the cornea of ​​a subject through an air jet nozzle to deform the cornea; measuring the amount of light reflected from the cornea to the air jet nozzle by emitting infrared light into the cornea through an infrared sensor; and converting the amount of light measured by the infrared sensor before and after corneal deformation into intraocular pressure.

[0014] The step of measuring light intensity may include the following process: emitting infrared light to the cornea through a light-emitting device, and receiving the light reflected from the cornea through light-receiving devices arranged on both sides of the light-emitting device to measure the light intensity.

[0015] Furthermore, after the step of ejecting compressed air to deform the cornea, a step may be included to receive the compressed air reflected from the cornea and measure the air pressure by a pressure sensor. In this case, the air pressure measured by the pressure sensor before and after corneal deformation and the amount of light measured by the infrared sensor can be correlated to convert into intraocular pressure.

[0016] The effects of the invention

[0017] According to the present invention, non-contact intraocular pressure measurement allows for hygienic use by the subject without causing discomfort. By integrating an infrared sensor into the nozzle module, the system can be miniaturized and made portable. Intraocular pressure can be accurately measured even on irregular corneal surfaces. Furthermore, the use of a relatively inexpensive infrared sensor facilitates easy development for home use. As a result, even in ordinary households, patients can pre-diagnose glaucoma and undergo regular eye examinations for early detection, thereby minimizing disease damage. Attached Figure Description

[0018] Figure 1 This is a perspective view of a non-contact portable intraocular pressure measurement system utilizing infrared intensity differences, according to an embodiment of the present invention.

[0019] Figure 2 To show Figure 1 A 3D view of the nozzle module extracted from it.

[0020] Figure 3 for Figure 2 The exploded perspective view of the nozzle module shown.

[0021] Figure 4 for Figure 2 The front view of the nozzle module shown.

[0022] Figure 5 For along Figure 4 A sectional view taken along line AA.

[0023] Figure 6 For along Figure 4 A sectional view taken from the BB line.

[0024] Figure 7 This is a structural diagram illustrating an example of a pressure sensor. Detailed Implementation

[0025] The present invention will now be described in detail with reference to the accompanying drawings. The same reference numerals are used for the same structures, and repeated descriptions and detailed descriptions of well-known functions and structures that may unnecessarily obscure the spirit of the invention will be omitted. Embodiments of the invention are provided to provide a more complete description of the invention to those skilled in the art. Therefore, for clarity, the shapes and dimensions of elements in the drawings may be exaggerated.

[0026] Figure 1 This is a perspective view of a non-contact portable intraocular pressure measurement system utilizing infrared intensity differences, according to an embodiment of the present invention. Figure 2 To show Figure 1 A 3D view of the nozzle module extracted from it. Figure 3 for Figure 2 The exploded perspective view of the nozzle module shown. Figure 4 for Figure 2 The front view of the nozzle module shown. Figure 5 For along Figure 4 A sectional view taken along line AA. Figure 6 For along Figure 4 A sectional view taken from the BB line.

[0027] Reference Figures 1 to 6 A non-contact portable intraocular pressure measurement system 100 utilizing infrared intensity differences according to an embodiment of the present invention includes a nozzle module 110, an infrared sensor 120, and a controller 130.

[0028] The nozzle module 110 receives compressed air from the compressed air supply source 140 and sprays it onto the cornea 10 of the subject through the air jet port 111 to deform the cornea 10. The compressed air supply source 140 draws in and compresses the air before supplying it to the nozzle module 110.

[0029] For example, the compressed air supply source 140 may include an air compressor and valves. The air compressor may be configured as a diaphragm type, which draws in and compresses external air through an inlet via a filter as an elastic plate of an internal diaphragm reciprocates via a motor.

[0030] When the air compressor outlet is opened or closed, the valve can selectively supply compressed air to the air compressor. The air compressor and valve can be controlled by controller 130. Nozzle module 110 can be installed externally to and connected to compressed air supply source 140.

[0031] An infrared sensor 120 is disposed within the nozzle module 110 to measure the amount of light reflected from the cornea 10 by emitting infrared light towards the cornea 10. Infrared light is an electromagnetic wave with a wavelength longer than visible light.

[0032] Infrared sensor 120 is configured to emit infrared light with a wavelength within a range that does not damage the cornea 10. As infrared sensor 120 emits infrared light toward the cornea 10, intraocular pressure can be measured while preventing glare for the subject.

[0033] Because the infrared sensor 120 detects the amount of infrared light reflected from the surface of the cornea 10 by irradiating the entire surface of the cornea 10 with infrared light, it can accurately measure intraocular pressure even if the surface of the cornea 10 is irregular.

[0034] The controller 130 converts the amount of light measured by the infrared sensor 120 before and after the deformation of the cornea 10 into intraocular pressure. When compressed air is applied to the cornea 10, the cornea 10 deforms, and the curvature of the corneal surface changes according to the degree of deformation. The change in curvature of the corneal surface caused by the intraocular pressure alters the path of infrared light reflected from the cornea 10, thereby producing a difference in the amount of infrared light detected by the infrared sensor 120.

[0035] Therefore, the controller 130 can use a correlation model representing the relationship between infrared light intensity and intraocular pressure to convert the light intensity measured by the infrared sensor 120 before and after the deformation of the cornea 10 into intraocular pressure, thereby determining whether it is glaucoma or the like.

[0036] The controller 130 can be installed externally to the compressed air supply source 140. Alternatively, the controller 130 can be built into the compressed air supply source 140. The controller 130 can receive system on / off commands and intraocular pressure measurement start commands from the user via the user interface 131 to control the non-contact portable intraocular pressure measurement system 100 as a whole, such as controlling the compressed air supply source 140 and the infrared sensor 120. The controller 130 can display the measured intraocular pressure on the display 136.

[0037] As described above, the non-contact portable intraocular pressure measurement system 100 allows for hygienic use by the subject without any discomfort through non-contact intraocular pressure measurement. By integrating the infrared sensor 120 into the nozzle module 110, the system can be miniaturized and made portable. Furthermore, it can accurately measure intraocular pressure even on irregular corneal surfaces. The use of the relatively inexpensive infrared sensor 120 facilitates its development for home use. Consequently, even in ordinary households, patients can pre-diagnose glaucoma and undergo regular eye examinations for early detection, thereby minimizing disease damage.

[0038] On the other hand, the infrared sensor 120 may include a sensor support block 121, a light-emitting device 122, and a pair of light-receiving devices 123.

[0039] A sensor support block 121 is disposed within the nozzle module 110. The sensor support block 121 may include a head 121a and a body 121b. The head 121a may have a shape in which the outer diameter decreases towards the front end, which faces the cornea 10. That is, the head 121a may be tapered towards the front end, which faces the cornea 10. The head 121a may have a groove that curves in a hemispherical or dome shape from the front end.

[0040] Within the front end groove of the block 121a, the light-emitting portion of the light-emitting device 122 is exposed, and each light-receiving portion of the light-receiving device 123 is exposed. Furthermore, when multiple pressure sensors 150 are further provided, each sensing portion of the multiple pressure sensors 150 is exposed within the front end groove of the block 121a. Therefore, the front end groove of the block 121a transmits infrared light reflected from the cornea 10 to the light-receiving device 123 by maximizing the collection of infrared light, and also transmits compressed air reflected from the cornea 10 to the multiple pressure sensors 150 by maximizing the collection of compressed air.

[0041] The block body 121b can be coaxially connected to the rear end of the block head 121a in a cylindrical shape, the outer diameter of which is smaller than the maximum outer diameter of the block head 121a. Therefore, the boundary between the block body 121b and the block head 121a can be stepped. Thus, in the sensor support block 121, when the block body 121b is inserted into the insertion groove of the nozzle body 112, the step is located around the insertion groove of the nozzle body 112, and can be stably supported by the nozzle body 112. Furthermore, the step of the sensor support block 121 can be bonded to the area around the insertion groove of the nozzle body 112 using an adhesive or the like.

[0042] The light-emitting device 122 is supported by the sensor support block 121 to emit infrared light toward the cornea 10. The light-emitting device 122 may be formed of an infrared-emitting diode or the like. The light-emitting device 122 can be driven and controlled by the controller 130.

[0043] The light-emitting device 122 can be installed such that its light-emitting portion is exposed through the center of the front groove of the block head 121a, and extends through the sensor support block 121 in the front-rear direction. The sensor support block 121 can expose the light-emitting portion of the light-emitting device 122 through an exposure hole, the diameter of which is smaller than the diameter of the hole in the body into which the light-emitting device 122 is inserted.

[0044] A pair of light-receiving devices 123 are respectively disposed on both sides of the light-emitting device 121 and supported by the sensor support block 121 to receive light reflected from the cornea 10 to measure the amount of light. The light-receiving devices 123 can be formed of photodiodes or the like. The light-receiving devices 123 can convert the measured amount of light into an electrical signal and provide it to the controller 130.

[0045] That is, the light-receiving device 123 can measure the amount of light before and after the deformation of the cornea 10 and convert it into an electrical signal to provide to the controller 130. The controller 130 can convert the electrical signal provided by the light-receiving device 123 before and after the deformation of the cornea 10 into intraocular pressure.

[0046] The light-receiving device 123 can be installed such that each light-receiving portion is exposed through the center of the front groove of the block head 121a and passes through the sensor support block 121 in a state inclined towards the center with reference to the front-back direction. The light-receiving device 123 can be configured to be symmetrical about the light-emitting device 121. Therefore, the light-receiving device 123 can receive the maximum amount of infrared light reflected from the cornea 10.

[0047] For accurate measurement of intraocular pressure, initial alignment of the nozzle module 110 with the cornea 10 is important. When the nozzle module 110 is initially positioned relative to the cornea 10, the voltage difference measured from a pair of light-receiving devices 123 can be used for the initial alignment of the nozzle module 110 with respect to the cornea 10.

[0048] For example, when the voltage difference measured from the light-receiving device 123 is determined to be within the allowable range, the controller 130 recognizes that the nozzle module 110 is located at the target position relative to the cornea 10, and can then drive the compressed air supply source 140. When the voltage difference measured from the light-receiving device 123 is determined to be outside the allowable range, the controller 130 can guide the subject to position the nozzle module 110 relative to the cornea 10 at the target position via an alarm or the like.

[0049] On the other hand, the nozzle module 110 may include a nozzle body 112 and a nozzle tip 113.

[0050] In the nozzle body 112, a sensor support block 121 is fixed at the center, and an air supply port 114 for receiving compressed air from the compressed air supply source 140 is formed at the edge. The nozzle body 112 may have a shape having a central part 112a, a first diameter expansion part 112b, and a second diameter expansion part 112c.

[0051] The central portion 112a of the main body has an insertion groove at its center for inserting the block body 121b of the sensor support block 121 from the front. The central portion 112a of the main body may be a hollow cylinder with an opening at the front. A step is formed along the bottom edge of the insertion groove of the central portion 112a, which can be supported by placing the rear end of the block body 121b on the step. Multiple holes may be formed on the bottom surface of the insertion groove of the central portion 112a for leading out each lead of the light-emitting device 122, the light-receiving device 123, and the multiple pressure sensors 150.

[0052] The first enlarged diameter portion 112b is formed along the outer periphery of the main body center portion 112a, closer to the rear end side, and has a larger outer diameter than the main body center portion 112a. The air supply port 114 can be formed to extend through the first enlarged diameter portion 112b in the front-rear direction. The air supply port 114 can be shaped to be tangential to the side of the first enlarged diameter portion 112b. Two air supply ports 114 can be provided and can be arranged symmetrically about the first enlarged diameter portion 112b. An air supply pipe 114a for connecting to a compressed air supply source 140 can be installed at the air supply port 114.

[0053] The first diameter expansion portion 112b and the front end portion of the main body center portion 112a together form an air flow path between the nozzle tip 113 and the inner peripheral surface of the nozzle tip 113, thereby allowing compressed air flowing in from the air supply port 114 to be transferred to the air injection port 111 of the nozzle tip 113.

[0054] The second enlarged diameter portion 112c is formed along the outer periphery of the main body center portion 112a with a larger outer diameter than the first enlarged diameter portion 112b, relative to the rear end of the main body center portion 112a. The second enlarged diameter portion 112c may form a step between itself and the first enlarged diameter portion 112b and support the rear end of the nozzle tip 113. The step of the second enlarged diameter portion 112c may be bonded to the rear end of the nozzle tip 113 using an adhesive or the like.

[0055] An air injection port 111 is formed at the center of the nozzle tip 113, thereby housing the sensor support block 121 together with the nozzle body 112. Compressed air supplied through the air supply port 114 is received between the nozzle tip 113 and the nozzle body 112, and then ejected through the air injection port 111. The nozzle tip 113 may have a first tip 113a and a second tip 113b. The first tip 113a is a hollow cylinder with openings at the front and rear ends, and the rear end can be supported by contacting the step of the second expanded diameter portion 112c.

[0056] The second pointed tip 113b may be shaped such that its outer diameter decreases from the front end of the first pointed tip 113a toward the cornea 10. That is, the second pointed tip 113b may be tapered toward the front end, which faces the cornea 10. The cone angle of the second pointed tip 113b is the same as the cone angle of the block 121a, such that a predetermined interval is formed between the inner surface of the second pointed tip 113b and the outer surface of the block 121a.

[0057] An air injection port 111 is formed at the center of the front end of the second tip 113b. The air injection port 111 may be circular. The air injection port 111 may have a diameter that exposes the front end of the block 121a. Compressed air flowing into the nozzle body 112 can move uniformly along the flow path between the first tip 113a and the block 121a to the air injection port 111, and then be injected in an annular shape through the air injection port 111.

[0058] On the other hand, a non-contact portable intraocular pressure measurement system may include a pressure sensor 150. The pressure sensor 150 is disposed within the nozzle module 110 to receive compressed air ejected from the nozzle module 110 and reflected from the cornea 10 to measure air pressure.

[0059] When compressed air is applied to the cornea 10, the cornea 10 deforms, changing the distance difference between the cornea 10 and the pressure sensor 150, thereby altering the air pressure difference detected by the pressure sensor 150. The controller 130 can use a correlation model representing the relationship between air pressure and intraocular pressure to convert the air pressure measured by the pressure sensor 150 before and after the deformation of the cornea 10 into intraocular pressure.

[0060] A pair of pressure sensors 150 may be provided. In each pressure sensor 150, the sensing portion is exposed at the center of the front groove of the head 121a between the light-receiving devices 123, and can be mounted to pass through the sensor support block 121 in a state of tilting towards the center based on the back-to-foreground direction. The pressure sensor 150 can be configured to be symmetrical about the light-emitting device 122. Therefore, the pressure sensor 150 can receive the maximum amount of compressed air reflected from the cornea 10. Each pressure sensor 150 can be configured to be spaced at the same interval from the light-receiving devices 123 on both sides.

[0061] As an example, such as Figure 7 As shown, the pressure sensor 150 can be constructed as a piezoresistive pressure sensor comprising a diaphragm 151 and a piezoresistor 152. The diaphragm 151 deforms due to compressed air reflected from the cornea 10. The piezoresistor 152 converts the resistance value according to the amount of deformation of the diaphragm 151, thereby allowing the measurement of the compressed air pressure.

[0062] The pressure sensor 150 can provide the measured air pressure to the controller 130 by converting it into an electrical signal. That is, the pressure sensor 150 can measure the amount of light before and after the deformation of the cornea 10 and convert it into an electrical signal to provide to the controller 130. The controller 130 can convert the electrical signal provided by the pressure sensor 150 before and after the deformation of the cornea 10 into intraocular pressure.

[0063] The controller 130 can correlate the air pressure measured by the pressure sensor 150 and the light intensity measured by the infrared sensor 120 before and after the deformation of the cornea 10 to calculate intraocular pressure. For example, the controller 130 can supplement the intraocular pressure value in various ways to increase the ability to distinguish intraocular pressure, such as by averaging the values ​​of the air pressure measured by the pressure sensor before and after the deformation of the cornea 10 and the values ​​of the light intensity measured by the infrared sensor 120, or by selecting the maximum value, etc.

[0064] An embodiment of the present invention provides a method for measuring intraocular pressure using differences in infrared intensity as follows.

[0065] First, compressed air is injected into the subject's cornea through an air jet nozzle to deform the cornea.

[0066] Then, the amount of light reflected from the cornea to the air jet is measured by emitting infrared light towards the cornea using an infrared sensor. In this case, infrared light can be emitted towards the cornea by a light-emitting device, and the amount of light can be measured by receiving the light reflected from the cornea by light-receiving devices arranged on both sides of the light-emitting device.

[0067] Then, the amount of light measured by the infrared sensor before and after corneal deformation is converted into intraocular pressure. Further, compressed air reflected from the cornea can be received to measure air pressure via a pressure sensor. In this case, the air pressure measured by the pressure sensor before and after corneal deformation and the amount of light measured by the infrared sensor can be correlated to convert into intraocular pressure.

[0068] Although the invention has been described with reference to one embodiment shown in the accompanying drawings, this is merely exemplary, and those skilled in the art will understand that various modifications and equivalent embodiments can be made therefrom. Therefore, the true scope of protection of the invention should be determined by the appended claims.

Claims

1. A non-contact portable intraocular pressure measurement system utilizing infrared intensity differences, characterized in that, include: The nozzle module receives compressed air from a compressed air supply source and sprays the compressed air onto the cornea of ​​the subject through an air jet nozzle to deform the cornea. An infrared sensor, disposed within the nozzle module, measures the amount of light reflected from the cornea by emitting infrared light towards the cornea. The sensor includes: a sensor support block disposed within the nozzle module; a light-emitting device supported by the sensor support block to emit infrared light towards the cornea; and a pair of light-receiving devices, respectively disposed on either side of the light-emitting device and supported by the sensor support block, to receive light reflected from the cornea and measure the amount of light. The controller is used to convert the amount of light measured by the aforementioned infrared sensor before and after corneal deformation into intraocular pressure. The aforementioned sensor support block includes: a head, which is tapered towards its front end, the front end facing the cornea, the head having a groove that curves inward from the front end; and a body connected to the rear end of the head. The aforementioned light-emitting device can be installed in such a manner that, with its light-emitting portion exposed through the center of the front groove of the aforementioned block, it extends through the aforementioned sensor support block in the front-rear direction. The aforementioned light-receiving device can be installed in the following manner: each light-receiving part is exposed through the center of the front groove of the aforementioned block head, and passes through the aforementioned sensor support block in a state of inclination towards the center side with the front-back direction as a reference. The above-mentioned nozzle module includes: The nozzle body has the aforementioned sensor support block fixed at its center and an air supply port formed at its edge for receiving compressed air from the aforementioned compressed air supply source; and The nozzle tip, with the aforementioned air injection port formed at its center, houses the sensor support block together with the nozzle body. Compressed air supplied through the air supply port is received between the nozzle tip and the nozzle body and ejected through the air injection port. The above-mentioned nozzle tip has: The first pointed head, with openings at its front and rear ends; and The second pointed tip has an air jet nozzle formed at the center of its front end and is tapered toward the front end, with the front end facing the cornea, thereby injecting compressed air in an annular pattern between itself and the block.

2. The non-contact portable intraocular pressure measurement system utilizing infrared intensity differences according to claim 1, characterized in that, The nozzle module includes a pressure sensor disposed within it to receive compressed air ejected from the nozzle module and reflected from the cornea to measure air pressure. The controller converts intraocular pressure by correlating the air pressure measured by the pressure sensor before and after corneal deformation with the amount of light measured by the infrared sensor.

3. A method for measuring intraocular pressure using the non-contact portable intraocular pressure measurement system based on infrared intensity differences as described in claim 1, characterized in that, include: The step of deforming the cornea by spraying compressed air into the cornea of ​​the subject through an air jet nozzle; The step of measuring the amount of light reflected from the cornea to the air jet nozzle by emitting infrared light into the cornea using an infrared sensor; as well as The step involves converting the amount of light measured by an infrared sensor before and after corneal deformation into intraocular pressure.

4. The intraocular pressure measurement method based on infrared intensity differences according to claim 3, characterized in that, The steps for measuring light intensity include the following process: The amount of light is measured by emitting infrared light into the cornea through a light-emitting device and receiving the light reflected from the cornea through light-receiving devices arranged on both sides of the light-emitting device.

5. The method for measuring intraocular pressure using infrared intensity differences according to claim 3, characterized in that, After the above steps of spraying compressed air to deform the cornea, This includes the step of receiving compressed air reflected from the cornea to measure air pressure via a pressure sensor. In the above steps of converting to intraocular pressure, Intraocular pressure is calculated by correlating the air pressure measured by a pressure sensor before and after corneal deformation with the amount of light measured by an infrared sensor.

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