Light feeding instrument

Abstract

The utility model discloses a light feeding instrument to solve the problem that retina light damage is possibly caused after long-term use in the prior art, and meanwhile, the treatment effect is also improved. Compared with the prior art in which only parameters such as red light source power and emergent light beam size are concerned, the utility model focuses on the important index of irradiance (power density), emergent light is a collimated Gaussian beam and the optical characteristics of eyes (a human eye refraction system is equivalent to a convex lens with a focal length of 17.2 mm). An optical component diffuser is additionally arranged at the position close to the cornea of a user, so that a collimated Gaussian beam is converted into diffused light to enter the eyes of the user, and diffused light spots are formed on the retina, the treatment area is sufficient, energy distribution is uniform, it is ensured that the irradiance is at the expected safety magnitude, and meanwhile the actual treatment effect is ensured.

Description

Technical Field

[0001] The utility model relates to ophthalmic treatment equipment, in particular to a light feeding instrument. Background Art

[0002] Currently, flashing red light amblyopia treatment devices are widely used to treat amblyopia (especially hyperopic amblyopia) in adolescents. The principle is: the amblyopic eye is repeatedly stimulated by red light, combined with fine vision training, to treat paracentral fixation amblyopia. Because the fovea of the macula only has cone cells, which are sensitive to red light and can receive it, while rod cells are insensitive to red light, repeated stimulation of flashing red light can force the fovea to fixate, thereby inhibiting the paracentral fixation point.

[0003] In recent years, a class of light-feeding devices for myopia treatment has appeared on the market (such as Figure 1 (as shown), in essence, it mainly adjusts the working mode of the flashing red light amblyopia treatment device: the flashing red light stimulation is changed to irradiation lasting several minutes. Its theoretical basis is that red light with a wavelength between 630-650 nanometers can produce a series of photobiological effects when continuously irradiating vascular tissue, causing vasodilation, decreased blood viscosity, reduced red blood cell aggregation, and decreased concentrations of inflammatory mediators. Irradiating the retina with a safe power and effective time can dilate and thicken the choroidal blood vessels in the posterior pole of the eye, increase blood perfusion, improve its nutritional supply to the sclera, increase the collagen content in the interstitial matrix of the scleral fiber cells, and restore the strength and thickness of the thinned and expanded scleral fibers of the myopic eye, thereby effectively controlling the length of the eye axis and preventing the occurrence and increase of myopia.

[0004] As a new technology, the ophthalmology community is currently cautious about the use of the light-feeding device, and there have been sporadic reports of users experiencing microperipheral damage.

[0005] Professor He Mingguang and his team at the Sun Yat-sen University Eye Center recently conducted a multicenter randomized controlled trial to evaluate the effect of repeated low-level red-light therapy (Low-Level Red-Light Therapy) on controlling myopia progression in children. Their findings, "Effect of Repeated Low-Level Red-Light Therapy in Myopia Control in Children," were pre-published in Ophthalmology on November 24, 2021. The study showed that repeated low-level red-light therapy (Low-Level Red-Light Therapy) was effective in controlling myopia progression in children aged 8-13 years. As a new alternative treatment, red-light therapy has good user acceptance and no observed functional or structural damage; however, further research is needed to explore its long-term safety, efficacy, and optimal treatment options.

[0006] The inventors conducted an in-depth analysis of existing photoreceptors and the characteristics of their optical systems during use, and noticed that the design factors in current photoreceptor products are seriously neglected. After long-term use, they may cause retinal light damage and affect the actual treatment effect. Utility Model Content

[0007] The utility model provides a light feeding device to solve the problem that the actual effect of treating myopia in the prior art is not obvious and side effects may be caused after long-term use.

[0008] In order to achieve the above purpose, the present invention provides the following technical solutions:

[0009] A light-feeding instrument includes a light source device, a lens barrel and an eye mask. A first optical component is arranged in the lens barrel, and the 630-650 nanometer red light output by the first optical component is a collimated Gaussian beam; the eye mask is fixedly arranged at the light output end of the lens barrel; the special feature of the light-feeding instrument is that the light-feeding instrument also includes a second optical component, which is located on the output side of the first optical component and close to the user's cornea, and is used to convert the collimated Gaussian beam into a uniform diffuse light form to enter the user's eye.

[0010] Optionally, the second optical component is fixedly installed near the light outlet of the eye mask.

[0011] Optionally, the second optical component is fixedly mounted on the inner side of the light outlet of the eye mask, 0.5 cm to 5 cm away from the end face of the light outlet of the eye mask.

[0012] Optionally, the projection spot diameter of the collimated Gaussian light beam on the second optical component is 0.5-2 cm, and the second optical component is a diffuser (Lambert material or similar Lambert material), so that the emitted diffuse red light is projected on the retina in the form of a diffuse spot after passing through the eye refractive system, avoiding the exponential increase in irradiance caused by the collimated light beam focusing on the retina after passing through the convex lens system (human eye refractive system), thereby damaging the retinal tissue.

[0013] Optionally, the laser power output by the light source device is 0.2-2.0 mW.

[0014] The utility model has at least the following beneficial effects:

[0015] Compared with the existing technology that usually only focuses on parameters such as the power of the red light source and the size of the output beam, the present invention focuses on the important indicator of irradiance (power density), the output light is a collimated Gaussian beam and the optical characteristics of the eye (the human eye's refractive system is equivalent to a convex lens with a focal length of about 17.2 mm), and cleverly adds an optical component diffuser near the user's cornea to convert the collimated Gaussian beam into diffuse light that enters the user's eye and forms a diffuse light spot on the retina, so that the treatment area (the projection area of the red light on the retina) is sufficient and the energy distribution is uniform, ensuring that the retinal irradiance is at the expected safe level, improving safety, and at the same time improving the treatment effect. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] To more intuitively illustrate the prior art and the present invention, exemplary drawings are provided below. It should be understood that the specific shapes and structures shown in the drawings should not generally be considered as limiting conditions for implementing the present application; for example, based on the technical concepts disclosed in this application and the exemplary drawings, those skilled in the art are capable of easily making routine adjustments or further optimizations to the addition / reduction / attribution division, specific shapes, positional relationships, connection methods, dimensional ratios, etc. of certain units (components).

[0017] Figure 1 Schematic diagram of a light feeding instrument in the prior art;

[0018] Figure 2 A schematic diagram of an optical system when used in the prior art;

[0019] Figure 3 A schematic diagram of an optical system when using an embodiment of the present invention;

[0020] Figure 4 This is a simplified diagram for calculating optical parameters based on the Lambert diffuser;

[0021] Figure 5 A schematic diagram of a light-feeding device provided in one embodiment of the present invention.

[0022] Description of reference numerals:

[0023] 1-lens barrel; 2-eyecup; 3-simplified eye refractive system (including cornea, lens, etc.); 4-retina; 5-diffuser (diffuse transmissive glass or PC sheet, etc.). DETAILED DESCRIPTION

[0024] The present application will be further described below in detail through specific embodiments in conjunction with the accompanying drawings.

[0025] In the description of this application, "first," "second," etc. are intended to distinguish the objects referred to and do not have any special meaning in terms of technical connotation (for example, they should not be understood as emphasizing the degree of importance or order, etc.). Expressions such as "including," "comprising," and "having" also mean "not limited to" (certain units, components, materials, etc.).

[0026] First, a few terms in this field are briefly explained:

[0027] Light source device: generates a low-power collimated beam with a wavelength of 630-650 nanometers and can be configured with an optical pre-shaping component so that it can be coupled with the lens barrel.

[0028] Lens barrel: As the output channel of red light, it can usually also be provided with an optical shaping component (which can be recorded as the first optical component to distinguish it from the optical component newly added in this solution) to fix the distance between the eye and the light source.

[0029] Eye mask: Usually fixed at the light output end of the lens barrel to make it easier for patients to receive treatment and to assist in positioning. When in use, the patient's eye area skin contacts the eye mask, and the patient's eyes correspond to the two through holes of the eye mask (these two through holes are connected to the red light output channel of the lens barrel).

[0030] In addition, the light source device and the lens barrel can be separately arranged at the front and rear stages, or the light source device can be installed inside the lens barrel (at the rear of the lens barrel), and the specific form is not limited.

[0031] like Figure 1 As shown, the common light feeding device currently on the market generally includes a light source device, a lens barrel 1 and an eye mask 2. The light source device emits red light with a wavelength of 630-650 nanometers, which enters the lens barrel; when the patient uses it, the skin in the eye area contacts the eye mask, and the eyes are irradiated by the red light beam.

[0032] Table 1 lists various radiation parameters. Currently, the parameters of light therapy devices on the market are usually focused on radiation output (M) and output beam size (i.e., the size of the light spot projected on the light outlet end face of the eye mask). However, in reality, from the perspective of treatment safety, the irradiance (E) should be given more attention.

[0033] Table 1 Several parameters about radiation

[0034]

[0035] A photoreceptor usually uses a laser light source, which is shaped into a collimated Gaussian beam. Taking a typical photoreceptor product on the market as an example, based on the divergence angle of the collimated beam it emits, the collimated beam can be regarded as a beam emitted from a point light source 0.274m away from the eye. Then, the beam passes through the eye's refractive system (a convex lens with a focal length of ≈1 / 58=0.0172m) and will be focused at about 0.0183m on the opposite side of the eye's refractive system. Figure 2 As shown. Therefore, for the user, the light will converge exactly at the retinal plane. Specifically:

[0036] 1 / 0.274=3.64 (D), 0.274 meters is the far point distance of a -3.64D myopic eye (when the human eye is not adjusting, that is, a point light source 0.274 meters away from the human eye will be imaged (focused) on the retina when the eye is at rest;

[0037] When the human eye observes the light source within the monochromatic laser beam, the visual center tends to identify it as a point light source because it has almost no detailed features, and to adjust the retina to form the minimum circle of diffusion. At this time, considering the accommodative power of teenagers of about 10D, it means that from about 6.50D of hyperopia to about -3.64D of myopia, under the adjustment of the eye, an image of the "point light source" can be formed on the retina, that is, it converges into a point of light.

[0038] So, if Figure 2 As shown, after the light from the lens barrel passes through the simplified eye refractive system 3 and converges into a "point" on the retina 4, its irradiance (power density) increases exponentially!

[0039]

[0040] For example, P = 0.015w, E=190.986w / m 2 .

[0041] All tissues in the fovea are poor conductors of heat. The light and heat that are highly concentrated in a very small area cannot be transferred to the surrounding area in time, causing the local temperature to rise sharply. The highly concentrated radiation causes violent local photochemical reactions, and its cumulative effects are likely to exceed the threshold of tissue cell tolerance, causing thermal damage and photochemical damage.

[0042] Therefore, we realized that existing light-feeding devices are both dangerous and inefficient:

[0043] Danger: The fovea, the most functionally important and structurally fragile area of the retina, is exposed to extremely high irradiance of laser light.

[0044] Inefficiency: Almost all the energy is concentrated in a "point" at the fovea center. The real treatment target, the "choroid", is a tissue covering 3 / 4 of the eyeball wall and does not receive light stimulation of a sufficient effective area.

[0045] In response to the above problems, the inventors have proposed a simple, low-cost and effective solution: before the laser enters the eye, a second optical component diffuser 5 (a transmissive diffuser, such as a diffusely transmissive glass or PC sheet) is installed close enough to the cornea to allow the collimated laser beam to enter the eye in a diffused form. There are also solutions on the market that use a grating at the light output of the light source device, but the relevant manufacturers do not have a power adjustment potentiometer in their configured light source devices. The grating is used to block the laser radiation power reaching the eye plane to meet the prescribed medical device safety standards. However, since the grating is far away from the eyeball (about 15 cm), the actual projection formed on the retina is still a small dot, which cannot meet the sufficient irradiation area of the choroid. As a result, the light output power is the lowest among similar products.

[0046] like Figure 3 As shown in the figure, the changes of the collimated light beam after the diffuser is modified: the projection of the laser beam on the diffuse glass or PC sheet can be regarded as a luminous object placed at a very close distance in front of the cornea in optical calculations, and is projected on the retina as a large diffuse light spot. The area of the diffuse spot is positively correlated with the projection area of the laser beam on the diffuser and the divergence of the diffuser, and is negatively correlated with the distance from the eye, pupil size, myopia, near accommodation of the eye and the depth of the anterior chamber.

[0047] like Figure 4 As shown, according to the calculation of the Lambert diffuser, the transmitted light will spread in all directions and be evenly distributed in the entire hemisphere space. The brightness is the same in all directions, and the luminous intensity of the diffused light in all directions is always proportional to cosθ. The diffused light of the light spot on the diffuser obeys this law. Then, by integration, the light spot can be regarded as diffused in all directions from the center of the circle (the left end of "18mm" in the figure). Assuming that the diffuser is 10mm away from the pupil plane and the pupil diameter is 7mm, it can be calculated that θ = 0.19205, the laser power is 0.5~2.0mW, and the maximum P is taken. 总 =2mW, after reflection loss, the transmission P=1mW, then the limiting aperture of 7mm Take the emmetropia refractive system (convex lens with focal length ≈ 1 / 58 = 0.0172m), and the formula 1 / u + 1 / v = 1 / f shows that the focal point is 409.09 mm away from the refractive system. By analogy d / 7 = (409.09-23) / 409.09, the projection spot diameter d = 6.60644 mm, so the projection area S = 0.34 cm 2 , then the irradiance E=P` / S=1.12mW / ㎝ 2 .

[0048] Thus, the embodiment of the present utility model has the following advantages:

[0049] 1. The effective treatment area is sufficient and the energy distribution is uniform;

[0050] 2. Ensure that the irradiance is within the expected level, and safety is greatly improved;

[0051] 3. No longer "dazzling", children's compliance is better;

[0052] 4. Increased tolerance to abnormal power fluctuations.

[0053] For example, the laser power output by the light source device is 0.2-2.0 mW, and the diffuser is fixedly installed on the inner side of the light outlet of the eye mask, such as Figure 5 As shown, the diameter of the projection spot of the collimated Gaussian light beam on the second optical component is 0.5-2 cm at a distance of 0.5 cm to 5 cm from the light outlet end face of the eye mask. The diffuser made of Lambertian material or a material similar to Lambertian material allows the emitted diffuse red light to be projected onto the retina in the form of a diffuse spot after passing through the eye refractive system, thereby avoiding the exponential increase in irradiance caused by the focus of the collimated light beam on the retina after passing through the convex lens system (human eye refractive system), which may damage the retinal tissue.

[0054] For some light-feeding instruments, the end face of the light outlet is a curved surface. The 0.5cm-5cm here is the distance value range set according to the closest position between the end face of the light outlet and the diffuser.

[0055] The present application has been described in a relatively specific and detailed manner through general explanations and specific embodiments. It should be understood that, based on the technical concept of the present application, several conventional adjustments or further innovations may be made to these specific embodiments; however, as long as they do not depart from the technical concept of the present application, the technical solutions obtained by such conventional adjustments or further innovations also fall within the scope of protection of the claims of the present application.

Claims

1. A light-feeding device, comprising a light source device, a lens barrel, and an eye mask, wherein a first optical component is disposed in the lens barrel, and the 630-650 nm red light output by the first optical component is a collimated Gaussian beam; the eye mask is fixedly disposed at the light output end of the lens barrel; characterized in that: The laser power output by the light source device is 0.2-2.0mW; the light-feeding instrument also includes a second optical component, which is located on the output side of the first optical component and close to the user's cornea, and is used to make the collimated Gaussian light beam directly pass through the second optical component and be converted into a uniform diffuse light form to enter the user's eye; the projection spot diameter of the collimated Gaussian light beam on the second optical component is 0.5-2cm, and the second optical component is a diffuser, so that the emitted diffuse red light is projected onto the retina in the form of a diffuse spot after passing through the eye's refractive system, and the projection area on the retina is sufficient and the energy distribution is uniform.

2. The light-feeding device according to claim 1, characterized in that: The second optical component is fixedly installed near the light outlet of the eye mask.

3. The light-feeding device according to claim 2, wherein: The second optical component is fixedly installed on the inner side of the light outlet of the eye mask, 0.5 cm to 5 cm away from the end face of the light outlet of the eye mask.

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