CN110367924B - Subjective and objective integrated precise optometry device and optometry method - Google Patents
Subjective and objective integrated precise optometry device and optometry method Download PDFInfo
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Abstract
An objective and subjective integrated precise optometry device and an optometry method are composed of a left eye light path and a right eye light path. The monocular optical path includes: the system comprises an eye refraction objective measurement subsystem, an eye refraction correction subsystem, an eyeball positioning subsystem and a subjective visual function test subsystem; the eye refraction objective measurement subsystem objectively measures the refraction of the eyes so as to guide the inner focusing device to move back and forth along the optical axis to correct myopia or hyperopia and rotate the cylindrical lens pair to correct astigmatism; the examinee observes the built-in sighting target through the device, according to subjective visual sensation, the two-dot chain line frame portion is moved integrally to slightly adjust the defocusing size, the cylindrical mirror is rotated to slightly adjust the relative angle to synthesize the astigmatism size and the axial direction until the best subjective correction visual quality is obtained, and the monocular subjective refraction is completed. After the subjective refraction of the left eye and the right eye is finished, the optical paths of the left eye and the right eye are integrally moved along the direction vertical to the optical axis to carry out interpupillary distance adjustment, red-green and binocular adjustment balance processes are carried out, and finally, an optimal accurate refractive correction prescription for the two eyes is given.
Description
Technical Field
The invention relates to the technical field of optical measurement, in particular to an objective and subjective integrated precise optometry device and an optometry method.
Background
Uncorrected refractive errors (including myopia, hyperopia and astigmatism), and surgically untreated cataracts are the two leading causes of visual impairment (see document [ J ]. Ophthalmology2016;123 (5): 1036-1042). Accurate measurement of the degree of refractive error of the human eye, and determination of the optimal corrective prescription are critical to the performance of refractive correction for a patient.
Currently, the optometry procedure includes two steps of objective optometry and subjective optometry. Methods for objective refraction include shadowgraph and optometry and objective measurement of refractive errors of patients by means of professional equipment such as computer optometry, eye aberrometers and the like. On the basis, the subjective refraction is carried out by utilizing the trial frame insert or the comprehensive refractometer. Since objective refraction does not involve subjective feedback from the subject, the test results are often used as reference. The accuracy and repeatability of subjective refraction depends on the degree of fitting of the examinee, the level of the examinee and clinical experience to a great extent, so that the quality of the corrective prescription obtained based on the existing subjective refraction method is uneven. More importantly, the prior trial frame insert or the prior comprehensive optometry instrument adopts trial lenses with discrete degrees (step length of 0.25D) to carry out subjective optometry, has adjustment errors and cannot realize continuous and accurate optometry on the ametropia of human eyes.
Aiming at the problems that subjective and objective separation is achieved in the existing optometry means (different devices are adopted), subjective optometry human factors are greatly influenced, and the degree of a test lens is discontinuous, so that a chemical adjustment error exists, the invention provides a subjective and objective integrated precise optometry device and an optometry method, which can be used for simultaneously measuring binocular refraction, continuous subjective optometry, interpupillary distance measurement and visual function measurement (including but not limited to vision and stereoscopy), and realizing binocular subjective and objective integrated precise optometry.
Disclosure of Invention
The technical problem solved by the invention is as follows: the utility model provides an accurate optometry device of subjective and objective integral type and optometry method, solve current optometry means subjective and objective separation (adopt different equipment), subjective sense optometry human factor influence is big, the problem that the trial lens number of degrees is discontinuous has the rectification error, can objective measurement binocular refraction simultaneously, continuous subjective sense optometry, interpupillary distance measurement and visual function measurement (including but not limited to eyesight, stereovision), realize the accurate optometry of binocular subjective and objective integral type.
Therefore, the invention firstly provides an subjective and objective integrated precise optometry device which consists of a left eye optical path and a right eye optical path; the monocular optical path comprises a human eye refraction objective measuring subsystem, a human eye refraction correcting subsystem, an eyeball positioning subsystem and a subjective visual function testing subsystem; the eye refraction objective measurement subsystem is used for objective measurement of eye refraction; the human eye refractive correction subsystem comprises an inner focusing device and a rotatable cylindrical lens pair and is used for correcting the defocusing and the astigmatism of the human eye; the eyeball positioning subsystem comprises a pupil imaging device and is used for positioning eyeballs; and the subjective visual function testing subsystem comprises a visual target objective lens and a visual target display device and is used for testing the visual function during subjective refraction.
Preferably, the subjective and objective integrated precise optometry device can realize monocular subjective and objective optometry by adopting a single-path structure and can also realize binocular subjective and objective optometry by adopting a double-path structure.
Further preferably, said human eye refractive objective measurement subsystem is selected from the group consisting of wavefront measuring techniques, optometry techniques, bar-grid focusing optometry techniques, scheiner disc optometry techniques, and blade measuring optometry techniques.
Further preferably, the wavefront measuring technique is selected from a hartmann wavefront sensor based on a microlens array, a hartmann wavefront sensor based on a microprism array, a curvature wavefront sensor, a pyramid wavefront sensor.
Further preferably, the optotype display device is selected from a CRT display, a commercial projector, a liquid crystal display, a plasma display, an electroluminescence display, an organic light emitting display, a projection display device, and a printed visual chart.
Further preferably, the human refractive correction subsystem comprises a pair of cylindrical mirrors; the cylindrical mirror pair is arranged at the conjugate position of the pupils of the human eyes, the turning angle of a single cylindrical mirror in the cylindrical mirror pair is adjusted, the astigmatism of the human eyes is continuously corrected, and the distance of the lenses in the first relay telescope or the third relay telescope is adjusted, so that the defocus is continuously corrected.
Further preferably, the eye refractive correction subsystem adopts a rotating cylindrical mirror to correct the astigmatism of the eyes; the cylindrical mirror pair continuously corrects astigmatism of human eyes, and one pair of the cylindrical mirror pair is selected from a plano-concave/plano-convex cylindrical mirror pair, a plano-concave/plano-concave cylindrical mirror pair and a plano-convex/plano-convex cylindrical mirror pair with the same or different focal powers.
The invention also discloses an subjective and objective integrated accurate optometry method, which comprises the following steps:
1. starting a near-infrared beacon light source, wherein the near-infrared beacon light source emits light, the light is collimated by a collimating objective lens, reflected by a second spectroscope and a first spectroscope, and then enters human eyes after passing through a cylindrical mirror pair and a first relay telescope or a third relay telescope;
2. the light reflected by the fundus of the human eye enters the wavefront sensor through the first relay telescope or the third relay telescope, the cylindrical mirror pair, the first spectroscope and the second relay telescope to objectively measure the refractive error of the human eye;
3. compensating the defocusing of the human eyes by a human eye defocusing correction formula and an internal focusing mode according to the measured refractive error of the human eyes; respectively rotating the single cylindrical lens in the cylindrical lens pair around the optical axis according to the measured human eye refractive error, and compensating the human eye astigmatism through a human eye astigmatism correction formula and a single cylindrical lens rotation mode;
4. after the compensation of the refractive error of the human eye is finished, the sighting target display device displays the sighting target of a specific type, and the human eye observes and judges the specific sighting target displayed on the sighting target display device through the first relay telescope or the third relay telescope, the cylindrical mirror pair, the first spectroscope, the second spectroscope, the reflecting mirror and the sighting target objective lens;
5. finely adjusting the defocusing size according to subjective visual perception, and finely adjusting the relative angle of the rotating cylindrical mirror to synthesize the astigmatism size and the axial direction until the best corrected visual quality is obtained, so as to finish the subjective refraction of the monocular;
6. after the subjective refraction of the left eye and the right eye is finished, the left eye optical path and the right eye optical path are integrally moved along the direction vertical to the optical axis to carry out interpupillary distance adjustment, red-green and binocular adjustment balance processes are carried out, and finally, a binocular optimal accurate refraction correction prescription is given.
The human eye defocus correction formula is as follows:
wherein D is correctable defocus, f 1 、f 2 The focal lengths of the two lenses in the first relay telescope are respectively, d is the distance between the two lenses in the first relay telescope in the optical axis direction, and the continuous correction of the defocusing of the human eye is realized by changing the distance between the two image lenses in the first relay telescope in the optical axis direction.
The formula for correcting human eye astigmatism is as follows:
C＝2F c cos(a 1 -a 2 )
where C and φ are the correctable astigmatism and axial direction, respectively, fc is the astigmatism of a single cylindrical mirror in the cylindrical mirror pair, a 1 And a 2 Is the astigmatic axis direction of the two cylindrical mirrors; continuous correction of astigmatism of the human eye is achieved by rotating the single cylindrical mirrors in the cylindrical mirror pair respectively.
Compared with the prior art, the invention has the advantages that: the subjective and objective integrated precise optometry device and the method are provided for the first time, the objective refraction measurement technology is adopted to objectively measure the diopter of human eyes, the internal focusing device and the rotating cylindrical mirror are guided to respectively compensate the defocusing and the astigmatism of the human eyes, through observing the built-in sighting marks, a detected person finely adjusts the defocusing amount and the astigmatism size and the axial direction according to subjective visual perception to realize the subjective precise optometry, and on the basis, the red-green and binocular balance adjustment flow is carried out, and finally the optimal precise refraction correction prescription is given.
Drawings
Fig. 1 is a schematic diagram of an embodiment 1 of the objective-subjective integrated precision optometry device based on wavefront measurement technology.
Fig. 2 is a schematic diagram of embodiment 2 of the subjective and objective integrated precise optometry device based on the wavefront measurement technology.
The labels in the figure are: 1. the human eye; 2. a pupil imaging device; 3. a first relay telescope; 4. a pair of cylindrical mirrors; 5. a first beam splitter; 6. a second relay telescope; 7. a wavefront sensor; 8. a visual target display device; 9. a near-infrared beacon light source; 10. a collimating objective lens; 11. an optotype objective lens; 12. a mirror; 13. a second spectroscope; 14. a first reflector; 15. a first lens; 16. a second reflector; 17. a third reflector; 18. a second lens; 19. a fourth mirror.
Detailed Description
The present invention will be described in further detail with reference to the following detailed description and accompanying drawings. It should be emphasized that the following description is merely exemplary in nature and is not intended to limit the scope of the invention or its application. Moreover, in the following description, descriptions of well-known structures and techniques are omitted so as to not unnecessarily obscure the concepts of the present invention.
Example 1
As shown in fig. 1, an objective and subjective integrated precision optometry device based on a wavefront measurement technology includes a pupil imaging device 2, a first relay telescope 3, a cylindrical mirror pair 4, a first spectroscope 5, a second relay telescope 6, a wavefront sensor 7, a sighting target display device 8, a near-infrared beacon light source 9, a collimating objective 10, a sighting target objective 11, a reflecting mirror 12, and a spectroscope 13.
The light emitted by the near-infrared beacon light source 9 is collimated by the collimating objective 10, reflected by the second spectroscope 13 and the first spectroscope 5, and enters the human eye 1 through the cylindrical mirror pair 4 and the first relay telescope 3; the light reflected by the fundus of the human eye 1 enters a wavefront sensor 7 through a first relay telescope 3, a cylindrical mirror pair 4, a first spectroscope 5 and a second relay telescope 6 to objectively measure the human eye refractive error (defocusing, astigmatism and astigmatism axial direction); integrally moving a double-dotted line frame part along the optical axis direction according to the measured refraction error of the human eyes (as marked in figure 1), and compensating the defocusing of the human eyes by adopting an internal focusing mode; and respectively rotating the single cylindrical mirrors in the cylindrical mirror pair 4 around the optical axis according to the measured refractive error of the human eyes, and compensating the astigmatism of the human eyes by adopting a cylindrical mirror synthesis mode. After the compensation of the human eye refractive error is completed, the sighting target display device 8 displays the sighting target of a specific type, and the human eye observes the sighting target displayed on the sighting target display device 8 through the middle first relay telescope 3, the cylindrical mirror pair 4, the first spectroscope 5, the second spectroscope 13, the reflecting mirror 12 and the sighting target objective lens 11.
According to subjective visual perception, the two-point line frame part is moved integrally to finely adjust the defocusing size (as marked in figure 1), and the relative angle of the rotating cylindrical mirror is finely adjusted to the astigmation size and the axial direction until the best subjective correction visual quality is obtained, so that the monocular subjective refraction is completed.
After the subjective refraction of the left eye and the right eye is finished, the left eye optical path and the right eye optical path are integrally moved along the direction vertical to the optical axis to carry out interpupillary distance adjustment, red-green and binocular adjustment balance processes are carried out, and finally, a binocular optimal accurate refraction correction prescription is given.
The human eye defocus correction formula is as follows:
wherein D is correctable defocus, f 1 、f 2 Are respectively provided withD is the distance between the two lenses in the relay telescope 3 in the direction of the optical axis. As can be seen from equation 1, by changing the distance between the two lenses in the relay telescope 3 on the optical axis, continuous correction of defocus of the human eye can be achieved.
The formula for correcting astigmatism of human eyes is as follows:
C＝2F c cos(a 1 -a 2 ) (2)
wherein C and phi are respectively the magnitude and axial direction of correctable astigmatism, F c The size of astigmatism of a single cylindrical mirror in a cylindrical mirror pair, a 1 And a 2 Is the astigmatic axis of the two cylindrical mirrors. As can be seen from formula 2, continuous correction of astigmatism of the eye can be achieved by rotating the single cylindrical mirrors in the pair of cylindrical mirrors, respectively.
Example 2
As shown in fig. 2, an objective and subjective integrated precision optometry device based on a wavefront measurement technology includes a pupil imaging device 2, a third relay telescope, a cylindrical mirror pair 4, a first spectroscope 5, a second relay telescope 6, a wavefront sensor 7, a sighting target display device 8, a near-infrared beacon light source 9, a collimating objective 10, a sighting target objective 11, a reflector 12, and a second spectroscope 13; wherein either the third relay telescope comprises a first mirror 14, a first lens 15, a second mirror 16, a third mirror 17, a second lens 18 and a fourth mirror 19.
Light emitted by the near-infrared beacon light source 9 is collimated by the collimating objective lens 10, reflected by the second spectroscope 13 and the first spectroscope 5, and enters the human eye 1 through the cylindrical mirror pair 4 or the third relay telescope; the light reflected by the fundus of the human eye 1 passes through the third relay telescope, the cylindrical lens pair 4, the first spectroscope 5 and the second relay telescope 6 to enter the wavefront sensor 7 to objectively measure the refractive error (defocus, astigmatism and astigmatism axis direction) of the human eye.
According to the measured refractive error of the human eye, synchronously moving a reflector 16 and a reflector 17 along the optical axis direction, and compensating the defocusing of the human eye by adopting an internal focusing mode; and respectively rotating the single cylindrical mirrors in the cylindrical mirror pair 4 around the optical axis according to the measured refractive error of the human eyes, and compensating the astigmatism of the human eyes by adopting a cylindrical mirror synthesis mode.
After the compensation of the refractive error of the human eye is completed, the sighting target display device 8 displays the sighting target of a specific type, and the human eye observes the sighting target displayed on the sighting target display device 8 through the third relay telescope, the cylindrical mirror pair 4, the first spectroscope 5, the second spectroscope 13, the reflecting mirror 12 and the sighting target objective lens 11 to perform subjective refraction. The examinee finely adjusts the defocusing of human eyes by synchronously moving the second reflector 16 and the third reflector 17, and simultaneously finely adjusts the astigmatism of human eyes by respectively rotating the cylindrical mirrors in the single cylindrical mirror pair 4 around the optical axis until the optimal visual effect is achieved, and the subjective refraction is finished and the optimal accurate refractive correction prescription is given.
In example 2, the human eye astigmatism is corrected in the same manner as in example 1. The correction of the defocusing of the human eye is realized by adopting a reflective third relay telescope. The device can also realize continuous correction of the defocusing of human eyes. Differs from example 1 in that f in equation 1 1 、f 2 And d are the focal lengths of the two lenses 15 and 18, respectively, and the distance between them.
The invention has thus been described with reference to the preferred embodiments. It should be understood by those skilled in the art that various other changes, substitutions, and additions may be made without departing from the spirit and scope of the invention. The scope of the invention is therefore not limited to the particular embodiments described above, but rather should be determined by the claims that follow.
Claims (7)
1. The utility model provides an accurate optometry device of subjective and objective integral type which characterized in that: the device consists of a left eye light path and a right eye light path; the monocular optical path comprises a human eye refraction objective measuring subsystem, a human eye refraction correcting subsystem, an eyeball positioning subsystem and a subjective visual function testing subsystem; the human eye refraction objective measurement subsystem is used for objective measurement of human eye refraction and comprises a first relay telescope or a third relay telescope, a cylindrical mirror pair, a first spectroscope, a second relay telescope, a wavefront sensor, a second spectroscope, a collimating mirror and a near-infrared beacon light source; the cylindrical mirror pair is arranged at the conjugate position of human eyes; the first relay telescope comprises two lenses; the third relay telescope comprises a first reflector, a first lens, a second reflector, a third reflector, a second lens and a fourth reflector; the human eye refraction correction subsystem is used for correcting the human eye defocusing and astigmatism and comprises an inner focusing device and a cylindrical lens pair, wherein the inner focusing device comprises a first relay telescope or a third relay telescope; the eyeball positioning subsystem is used for positioning eyeballs and comprises a pupil imaging device; the subjective visual function testing subsystem is used for testing visual functions during subjective refraction and comprises a first relay telescope or a third relay telescope, a cylindrical mirror pair, a first spectroscope, a second spectroscope, a reflector, a visual target objective and a visual target display device; the human eye refraction objective measuring subsystem and the main viewing function testing subsystem share part of optical devices; the cylindrical mirror pair of the refractive correction subsystem and the first relay telescope are both positioned in the common optical path of the human eye refractive objective measurement subsystem and the main viewing function test subsystem, or the cylindrical mirror pair of the refractive correction subsystem and the third relay telescope are both positioned in the common optical path of the human eye refractive objective measurement subsystem and the main viewing function test subsystem;
the subjective and objective integrated accurate optometry device performs optometry through the following steps:
1. the near-infrared beacon light source is started, emits light, is collimated by the collimating objective lens, is reflected by the second spectroscope and the first spectroscope, penetrates through the cylindrical lens pair, and enters human eyes through the first relay telescope or the third relay telescope;
2. the light reflected by the fundus of the human eye enters the wavefront sensor through the first relay telescope or the third relay telescope, the cylindrical lens pair, the first spectroscope and the second relay telescope, and the refractive error of the human eye is objectively measured;
3. compensating the human eye defocusing through a human eye defocusing correction formula and an internal focusing mode according to the measured human eye refractive error;
the human eye defocus correction formula is as follows: d = (D-f) 1 -f 2 )/f 1 f 2 WhereinD is correctable defocus, f 1 、f 2 The focal lengths of the two lenses in the first relay telescope are respectively, and d is the distance between the two lenses in the first relay telescope in the direction of the optical axis; or, f 1 、f 2 The focal lengths of the first lens and the second lens in the third relay telescope are respectively, and d is the distance between the first lens and the second lens in the optical axis direction; the continuous correction of the defocusing of the human eyes is realized by changing the distance between the two lenses in the first relay telescope or the third relay telescope on the optical axis;
respectively rotating a single cylindrical mirror in the cylindrical mirror pair around the optical axis to compensate the astigmatism of human eyes according to the measured refractive error of the human eyes;
the formula for correcting human eye astigmatism is as follows: c =2F c cos(a 1 -a 2 ), φ=(a 1 +a 2 )/2，
Where C and φ are the correctable astigmatism and axial direction, respectively, fc is the astigmatism of a single cylindrical mirror in the cylindrical mirror pair, a 1 And a 2 Is the astigmatic axial direction of the two cylindrical mirrors; continuous correction of astigmatism of the human eye is realized by respectively rotating the single cylindrical mirrors in the cylindrical mirror pair;
4. after the refractive error compensation of the human eye is finished, the sighting target display device displays the sighting target of a specific type, and the human eye observes and judges the specific sighting target displayed on the sighting target display device through the first relay telescope or the third relay telescope, the cylindrical mirror pair, the first spectroscope, the second spectroscope, the reflector and the sighting target objective lens;
5. and (3) finely adjusting the defocusing size according to subjective visual perception, and finely adjusting the relative angle by rotating the cylindrical mirror to synthesize the astigmatism size and the axial direction until the corrected visual quality with the best subjective is obtained, so that the monocular subjective vision optometry is completed.
2. The subjective and objective integrated precise optometry device according to claim 1, wherein: the device adopts a single-path structure to realize monocular subjective and objective optometry, or adopts a double-path structure to realize binocular subjective and objective optometry.
3. The subjective and objective integrated precise optometry device according to claim 1, wherein: the realization of the human eye refraction objective measuring subsystem is selected from a wavefront measuring technology, an optometry technology, a bar-grid focusing optometry technology, a Scheiner disc optometry technology and a blade measuring optometry technology.
4. The subjective and objective integrated precise optometry device according to claim 3, wherein: the wavefront measuring technique is selected from a Hartmann wavefront sensor based on a micro-lens array, a Hartmann wavefront sensor based on a micro-prism array, a curvature wavefront sensor, and a pyramid wavefront sensor.
5. The subjective and objective integrated precise optometry device according to claim 1, wherein: the cylindrical mirror pair is selected from a plano-concave/plano-convex cylindrical mirror pair, a plano-concave/plano-concave cylindrical mirror pair and a plano-convex/plano-convex cylindrical mirror pair with the same or different focal powers.
6. The subjective and objective integrated precise optometry device according to claim 1, wherein: in the human eye refractive objective measurement subsystem, the cylindrical mirror pair is arranged between the first relay telescope and the first spectroscope, or the cylindrical mirror pair is arranged between the third relay telescope and the first spectroscope; the cylindrical mirror pair is coaxial with the optical path of the first relay telescope or the third relay telescope, the primary optical path of the first spectroscope is coaxial with the optical path of the second relay telescope, the light splitting path of the first spectroscope is coaxial with the primary optical path of the second spectroscope, the light splitting path of the second spectroscope is coaxial with the optical path of the collimating objective lens, the near-infrared beacon light source is arranged at the rear position of the collimating objective lens, and the wavefront sensor is arranged at the rear position of the second relay telescope.
7. The subjective and objective integrated precise optometry device according to claim 1, wherein: the subjective visual function testing subsystem is used for measuring the visual functions of single eye and double eyes; the visual target display device is selected from CRT display, commercial projector, liquid crystal display, plasma display, electroluminescent display, organic light emitting display, projection display device, and printing visual chart.
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| PCT/CN2020/075652 WO2021031538A1 (en) | 2019-08-22 | 2020-02-18 | Subjective and objective integrated precise optometry device, and optometry method |
| US17/753,157 US20220330820A1 (en) | 2019-08-22 | 2020-02-18 | Subjective and objective integrated precise optometry device, and optometry method |
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| CN112754420A (en) * | 2021-01-08 | 2021-05-07 | 瑞尔明康(杭州)视光科技有限公司 | Wavefront aberration measurement system, associated visual perception learning training system and method |
| CN112754418A (en) * | 2021-01-08 | 2021-05-07 | 瑞尔明康(杭州)视光科技有限公司 | Portable binocular vision function training instrument |
| CN117357056A (en) * | 2023-11-03 | 2024-01-09 | 瑞尔明康(浙江)医疗科技有限公司 | Human eye measuring device and human eye measuring method |
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| EP2369972B1 (en) * | 2008-12-01 | 2017-06-07 | Perfect Vision Technology (HK) Ltd. | Methods and devices for refractive correction of eyes |
| JP2016220880A (en) * | 2015-05-29 | 2016-12-28 | 株式会社トプコン | Optometer |
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