CN117357056A - Human eye measuring device and human eye measuring method - Google Patents
Human eye measuring device and human eye measuring method Download PDFInfo
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- CN117357056A CN117357056A CN202311459837.8A CN202311459837A CN117357056A CN 117357056 A CN117357056 A CN 117357056A CN 202311459837 A CN202311459837 A CN 202311459837A CN 117357056 A CN117357056 A CN 117357056A
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- 238000000034 method Methods 0.000 title claims description 11
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- 210000001525 retina Anatomy 0.000 abstract description 4
- 230000004438 eyesight Effects 0.000 description 25
- 208000014733 refractive error Diseases 0.000 description 13
- 230000035945 sensitivity Effects 0.000 description 12
- 208000029091 Refraction disease Diseases 0.000 description 11
- 230000004430 ametropia Effects 0.000 description 11
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- 201000009310 astigmatism Diseases 0.000 description 3
- 230000004382 visual function Effects 0.000 description 3
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
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Abstract
The present disclosure provides a human eye measurement apparatus and a human eye measurement method. The human eye measuring device of the present disclosure includes a monocular measuring module including: a beacon light source for emitting an initial light; a first parallel light conversion device converting the initial light into parallel light; the light path adjusting component is used for adjusting the light path of the parallel light output by the first parallel light conversion device so as to irradiate the target human eyes; a target display, wherein a distance between a target image provided by the target display and a target human eye can be adjusted so that the target human eye generates different diopter responses; the Hartmann wavefront sensor is used for receiving retina reflected light from a target human eye in different diopter response states to measure wavefront aberration information; when the distance between the sighting target image and the target human eye is adjusted, the optical paths of the beacon light source and the target human eye are not adjusted.
Description
Technical Field
The present disclosure relates to the technical field of human eye diopter measurement, visual function measurement, and the like, and in particular, to a human eye measurement device and a human eye measurement method.
Background
Imaging and perception of the human eye is a fairly complex process, and human eye vision-related measurements are generally classified into objective ametropia (wavefront aberration) measurements and subjective vision function measurements.
The traditional objective measurement and subjective measurement are carried out step by adopting different equipment, the optometry process is greatly influenced by human factors, and in recent years, the technical proposal provides a subjective and objective integrated measurement method to solve the problem that the subjective and objective measurement equipment is not uniform (for example, chinese patent documents CN201910777661.8 and CN 202121357258.9), but the measurement of the subjective vision function is limited to the far vision measurement, and the diopter and the vision function of human eyes in different adjustment states cannot be measured.
The adjustment of eyes is fully relaxed when the far vision is checked, the adjustment of the parts to be used when the near vision and the middle vision are checked, three kinds of vision represent three different refractive states, and the human eye adjustment response is important to be related with the occurrence and the development of myopia, so that the human eye adjustment response is measured, and the eye refractive error can be judged primarily according to the change of the far vision, the visual function of the human eye can be estimated more fully.
Clinically, although the central vision is good, the contrast sensitivity is reduced, so that the contrast sensitivity examination and the near-far vision examination are particularly important in the subjective vision function examination.
Disclosure of Invention
The present disclosure provides a human eye measurement apparatus and a human eye measurement method.
According to one aspect of the present disclosure, there is provided a human eye measurement apparatus including a monocular measurement module including:
a beacon light source for emitting an initial light;
a first parallel light conversion device that converts the initial light into parallel light;
the light path adjusting component is used for adjusting the light path of the parallel light output by the first parallel light conversion device so as to irradiate the target human eyes;
a optotype display providing an optotype image with a distance from the target human eye that can be adjusted to cause the target human eye to produce different diopter responses;
a Hartmann wavefront sensor for receiving retinal reflected light from the target human eye in different diopter response states for wavefront aberration information measurement;
when the distance between the sighting target image and the target human eye is adjusted, the optical path between the beacon light source and the target human eye is not adjusted.
According to a human eye measurement device of at least one embodiment of the present disclosure, the monocular measurement module further includes:
and the optotype imaging objective lens is positioned between the optotype display and the target human eye so as to be beneficial to the target human eye to observe the optotype image.
According to a human eye measurement device of at least one embodiment of the present disclosure, the monocular measurement module further includes:
the driving mechanism can adjust the position of the sighting target display to adjust the distance between the sighting target image provided by the sighting target display and the target human eye.
According to a human eye measurement device of at least one embodiment of the present disclosure, the monocular measurement module further includes:
a focusing device for adjusting a distance between a target image provided by the target display and the target human eye by changing a position;
and a driving mechanism capable of driving the focusing device to cause the focusing device to change position.
A human eye measurement device according to at least one embodiment of the present disclosure, the focusing device includes a single lens, a transmissive/reflective lens group, or a variable focus liquid lens.
According to at least one embodiment of the present disclosure, the driving mechanism includes a motor and a transmission mechanism driven by the motor, so as to output a driving motion of the driving mechanism through the transmission mechanism.
According to a human eye measurement device of at least one embodiment of the present disclosure, the monocular measurement module further includes:
the refraction compensation module is configured in front of the target human eye to perform refraction compensation when the target human eye observes the sighting target image.
According to the human eye measuring device of at least one embodiment of the present disclosure, the retina reflected light from the target human eye in different diopter response states is received by the Hartmann wavefront sensor sequentially via the refraction compensation module and the optical path adjustment component to perform wavefront aberration information measurement.
A human eye measurement device according to at least one embodiment of the present disclosure, further comprising:
a computer device capable of controlling the amount of refractive compensation of the refractive compensation module based on wavefront aberration information measured by the Hartmann wavefront sensor.
According to at least one embodiment of the present disclosure, the refraction compensation module is capable of refraction compensation of the target human eye in different refraction response states while observing the optotype image.
The refractive compensation module comprises a transmissive/reflective 4f system in combination with a cylindrical lens group, a liquid lens, a flexible zoom lens, a anamorphic mirror, or a liquid crystal spatial light modulator, according to at least one embodiment of the present disclosure.
According to at least one embodiment of the present disclosure, the human eye measuring device is a monocular measuring device, or a binocular measuring device, and when the human eye measuring device is a binocular measuring device, it includes two monocular measuring modules symmetrically disposed to enable binocular measurement.
According to the human eye measuring device of at least one embodiment of the present disclosure, the two monocular measuring modules perform information processing and control based on the same computer apparatus.
According to another aspect of the present disclosure, there is provided a human eye measurement method, comprising:
monocular or binocular wavefront aberration measurement is carried out to obtain wavefront aberration information;
calculating and obtaining a monocular or binocular refraction compensation amount based on the wavefront aberration information;
wherein the wavefront aberration information measurements are made with monocular or binocular in different diopter response states.
The human eye measurement method according to at least one embodiment of the present disclosure further includes:
and calculating and obtaining the refraction compensation quantity of the monocular or binocular in different diopter response states based on the wavefront aberration information.
Drawings
The accompanying drawings, which are included to provide a further understanding of the disclosure and are incorporated in and constitute a part of this specification, illustrate exemplary embodiments of the disclosure and together with the description serve to explain the principles of the disclosure.
Fig. 1 is a block schematic diagram of a human eye measurement device of some embodiments of the present disclosure.
Fig. 2 is a block schematic diagram of a human eye measurement device of other embodiments of the present disclosure.
Fig. 3 is a flow chart of a human eye measurement method of some embodiments of the present disclosure.
Description of the reference numerals
100. Human eye measuring device
101. Beacon light source
102. First parallel light conversion device
103. Light path adjusting assembly
104. Visual target display
105. Hartmann wave-front sensor
106. Optotype imaging objective lens
107. Driving mechanism
108. Focusing device
109. Refraction compensation module
110. Computer equipment
111. Caliber matching module
200. The target human eye.
Detailed Description
The present disclosure is described in further detail below with reference to the drawings and the embodiments. It is to be understood that the specific embodiments described herein are merely illustrative of the relevant content and not limiting of the present disclosure. It should be further noted that, for convenience of description, only a portion relevant to the present disclosure is shown in the drawings.
In addition, embodiments of the present disclosure and features of the embodiments may be combined with each other without conflict. The technical aspects of the present disclosure will be described in detail below with reference to the accompanying drawings in conjunction with embodiments.
Unless otherwise indicated, the exemplary implementations/embodiments shown are to be understood as providing exemplary features of various details of some ways in which the technical concepts of the present disclosure may be practiced. Thus, unless otherwise indicated, features of the various implementations/embodiments may be additionally combined, separated, interchanged, and/or rearranged without departing from the technical concepts of the present disclosure.
The use of cross-hatching and/or shading in the drawings is typically used to clarify the boundaries between adjacent components. As such, the presence or absence of cross-hatching or shading does not convey or represent any preference or requirement for a particular material, material property, dimension, proportion, commonality between illustrated components, and/or any other characteristic, attribute, property, etc. of a component, unless indicated. In addition, in the drawings, the size and relative sizes of elements may be exaggerated for clarity and/or descriptive purposes. While the exemplary embodiments may be variously implemented, the specific process sequences may be performed in a different order than that described. For example, two consecutively described processes may be performed substantially simultaneously or in reverse order from that described. Moreover, like reference numerals designate like parts.
When an element is referred to as being "on" or "over", "connected to" or "coupled to" another element, it can be directly on, connected or coupled to the other element or intervening elements may be present. However, when an element is referred to as being "directly on," "directly connected to," or "directly coupled to" another element, there are no intervening elements present. For this reason, the term "connected" may refer to physical connections, electrical connections, and the like, with or without intermediate components.
For descriptive purposes, the present disclosure may use spatially relative terms such as "under … …," under … …, "" under … …, "" lower, "" above … …, "" upper, "" above … …, "" higher "and" side (e.g., in "sidewall") to describe one component's relationship to another (other) component as illustrated in the figures. In addition to the orientations depicted in the drawings, the spatially relative terms are intended to encompass different orientations of the device in use, operation, and/or manufacture. For example, if the device in the figures is turned over, elements described as "under" or "beneath" other elements or features would then be oriented "over" the other elements or features. Thus, the exemplary term "below" … … can encompass both an orientation of "above" and "below". Furthermore, the device may be otherwise positioned (e.g., rotated 90 degrees or at other orientations) and the spatially relative descriptors used herein interpreted accordingly.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting. As used herein, the singular forms "a", "an" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. Furthermore, when the terms "comprises" and/or "comprising," and variations thereof, are used in the present specification, the presence of stated features, integers, steps, operations, elements, components, and/or groups thereof is described, but the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof is not precluded. It is also noted that, as used herein, the terms "substantially," "about," and other similar terms are used as approximation terms and not as degree terms, and as such, are used to explain the inherent deviations of measured, calculated, and/or provided values that would be recognized by one of ordinary skill in the art.
Fig. 1 is a block schematic diagram of a human eye measurement device of some embodiments of the present disclosure. Fig. 2 is a block schematic diagram of a human eye measurement device of other embodiments of the present disclosure.
Referring to fig. 1 and 2, in some embodiments of the present disclosure, a human eye measurement device 100 of the present disclosure includes a monocular measurement module including:
a beacon light source 101, the beacon light source 101 for emitting an initial light (beacon light);
a first parallel light conversion device 102, the first parallel light conversion device 102 converting the initial light into parallel light;
the optical path adjusting component 103, the optical path adjusting component 103 performs optical path adjustment on the parallel light output by the first parallel light conversion device 102 to irradiate the target human eye;
the optotype display 104, the distance between the optotype image provided by the optotype display 104 and the target human eye can be adjusted to cause the target human eye 200 to produce different diopter responses;
a Hartmann wavefront sensor 105, the Hartmann wavefront sensor 105 for receiving retinal reflected light from a target human eye 200 in a different diopter response state for wavefront aberration information measurement;
when the distance between the optotype image and the target eye 200 is adjusted, the optical path between the beacon light source 101 and the target eye 200 is not adjusted.
The light source type of the beacon light source 101 may be an LD light source, an LED light source, an SLD light source, or the like, and the light source shape may be a point light source, an extended light source, or the like.
Referring to fig. 1 and 2, in some embodiments of the present disclosure, the distance between the target image provided by the target display 104 and the target human eye can be adjusted so that the target human eye 200 produces different diopter responses, and in turn, the hartmann wavefront sensor 105 can receive the retinal reflected light from the target human eye 200 in the different diopter response states for wavefront aberration information measurement. The present disclosure also designs the optical path of the whole eye measurement device 100, in the process that the distance between the optotype image and the target eye 200 is adjusted, the optical path between the beacon light source 101 and the target eye 200 is not adjusted, and more preferably, the optical path between the hartmann wavefront sensor 105 and the target eye 200 is not adjusted, so that the measuring optical path of the wavefront aberration information is more stable, and the measuring result is more accurate.
With continued reference to fig. 1 and 2, in some embodiments of the present disclosure, the human eye measurement device 100 of the present disclosure further comprises: the optotype imaging objective 106, the optotype imaging objective 106 is located between the optotype display 104 and the target eye 200 to facilitate viewing of the optotype image by the target eye 200. The optotype imaging objective 106 may be a convex lens or a combination of convex lenses, or the like.
Preferably, the optotype imaging objective 106 of the present disclosure is located outside the optical path of the beacon light source 101 and the target human eye 200, and is located outside the optical path of the Hartmann wavefront sensor 105 and the target human eye 200, avoiding unnecessary effects on the measurement of wavefront aberration information.
Referring to fig. 1, in some embodiments of the present disclosure, the human eye measurement device 100 of the present disclosure further includes:
a driving mechanism 107, the driving mechanism 107 being capable of adjusting the position of the optotype display 104 to adjust the distance between the optotype image provided by the optotype display 104 and the target human eye 200.
Referring to fig. 2, in other embodiments of the present disclosure, a human eye measurement device 100 of the present disclosure includes:
a focusing device 108, the focusing device 108 adjusting a distance between the target image provided by the target display 104 and the target human eye 200 by changing a position;
a driving mechanism 107, the driving mechanism 107 being capable of driving the focusing device 108 so that the focusing device 108 changes position.
Wherein the focusing means 108 comprises a single lens, a transmissive/reflective lens group, or a variable focus liquid lens, etc.
The present disclosure enables the target human eye 200 to generate different diopter responses when viewing the target image by adjusting the distance between the target image provided by the target display 104 and the target human eye 200, so that the Hartmann wavefront sensor 105 can measure wavefront aberration information of the target human eye 200 in different diopter response states.
For the drive mechanism 107 described in the present disclosure, it may include a motor and a transmission mechanism (e.g., a base) driven by the motor to output a driving action of the drive mechanism 107 through the transmission mechanism.
The motor may be a screw motor, the transmission mechanism may be a base that can be driven by a screw to perform reciprocating motion, the specific structure of the driving mechanism 107 is not particularly limited in the present disclosure, and those skilled in the art may adjust the specific implementation manner of the driving mechanism 107 under the teaching of the technical scheme of the present disclosure all fall within the protection scope of the present disclosure.
With continued reference to fig. 1 and 2, in some embodiments of the present disclosure, the human eye measurement device 100 of the present disclosure further comprises:
the refraction compensation module 109 is configured in front of the target human eye 200 to perform refraction compensation when the target human eye 200 observes the target image provided by the target display 104.
It should be noted that the refraction compensation module 109 of the present disclosure is located in the optical path between the Hartmann wavefront sensor 105 and the target human eye 200, in the optical path between the beacon light source 101 and the target human eye 200, and in the optical path between the optotype display 104 and the target human eye 200.
Based on the above configuration of the refraction compensation module 109, the human eye measurement device 100 of the present disclosure is capable of measuring wavefront aberration information of the target human eye 200 in different diopter response states.
Referring to fig. 1 and 2, in some embodiments of the present disclosure, retinal reflected light from a target human eye 200 in different diopter response states is received by a hartmann wavefront sensor 105 for wavefront aberration information measurement via a refraction compensation module 109, an optical path adjustment assembly 103, in sequence.
In some embodiments of the present disclosure, referring to fig. 1 and 2, the human eye measurement device 100 of the present disclosure further includes:
computer device 110 (a desktop computer, a portable computer, a handheld terminal device, an embedded device terminal, etc. having computing capabilities) computer device 110 is capable of controlling the amount of refractive compensation module 109 based on wavefront aberration information measured by Hartmann wavefront sensor 105.
The computer device 110 is capable of controlling the amount of refractive compensation of the refractive compensation module 109 based on wavefront aberration information measured by the Hartmann wavefront sensor 105. Calculating the refraction compensation amount based on the wavefront information difference information belongs to the prior art, and this disclosure is not repeated.
For example, the Hartmann wavefront sensor 105 may measure wavefront aberration information of the target human eye 200 in a fully relaxed state, from which the computer device 110 controls the refractive compensation module 109 to provide a corresponding amount of refractive compensation to effect correction of refractive errors (defocus, astigmatism, etc.) of the target human eye 200.
In some embodiments of the present disclosure, the refractive compensation module 109 of the human eye measurement device 100 of the present disclosure is capable of refractive compensation of a target human eye 200 in different diopter response states while viewing a optotype image.
The refraction compensation module 109 described in this disclosure may include, among other things, a transmissive/reflective 4f system in combination with a cylindrical lens group, a liquid lens, a flexible zoom lens, a anamorphic mirror, or a liquid crystal spatial light modulator, among others.
Fig. 1 and 2 show schematic block diagrams of structures of human eye measurement devices 100 according to various embodiments of the present disclosure, respectively.
It should be noted that, the specific structures shown in fig. 1 and fig. 2 are for explaining the technical solution of the human eye measurement device of the present disclosure in detail, and should not be construed as limiting the technical solution of the human eye measurement device of the present disclosure.
The human eye measurement device of the present disclosure is described in more detail below in conjunction with fig. 1 and 2.
Referring to fig. 1 and 2, the human eye measurement apparatus of the present disclosure can measure wavefront aberration information measurement and vision function measurement with a target human eye in different diopter response states (adjustment states).
The human eye measurement device 100 of the present disclosure preferably includes a beacon light source 101, a first parallel light conversion device 102 (e.g., a convex lens), a light path adjustment component 103 (e.g., a light splitting device, which may be composed of two light splitting mirrors disposed in parallel), a optotype display 104, a Hartmann wavefront sensor 105, an optotype imaging objective lens 106, a driving mechanism 107, a refraction compensation module 109, and a computer device 110.
The beacon light source 101, the first parallel light conversion device 102 (e.g. a convex lens), the optical path adjusting component 103, the optotype display 104, the hartmann wavefront sensor 105, the optotype imaging objective 106, the driving mechanism 107, and the refraction compensation module 109 form a monocular measurement module, and the two monocular measurement modules are symmetrically arranged to enable binocular measurement, and the two monocular measurement modules perform information processing and control based on the same computer device 110.
In some embodiments of the present disclosure, each monocular measurement module further includes an aperture matching module 111, the aperture matching module 111 being configured between the Hartmann wavefront sensor 105 and the optical path adjustment assembly 103, the aperture matching module 111 being configured to adjust a beam aperture of reflected light from the target human eye 200 reflected via the optical path adjustment assembly 103 to adapt to a detection aperture of the Hartmann wavefront sensor 105. The aperture matching module 111 of the present disclosure is preferably implemented by a lens group. Those skilled in the art may adjust or select the lens combination of the aperture matching module 111 in light of the technical solution of the present disclosure, which falls within the protection scope of the present disclosure.
Referring to fig. 2, in some embodiments of the present disclosure, each monocular measurement module further includes the focusing device 108 described above, the focusing device 108 adjusting the distance between the target image provided by the target display 104 and the target human eye 200 by changing positions.
In each monocular measurement module, light emitted by the beacon light source 101 is collimated into parallel light by the first parallel light conversion device 102, then enters the retina of the target human eye through the light path adjustment assembly 103 (light splitting device) and the refraction compensation module 109, light entering the fundus is reflected by the retina and returns to the light path adjustment assembly 103 (light splitting device) along the original light path, and then enters the Hartmann wavefront sensor 105 to finish wavefront aberration measurement in a completely relaxed state of the measured target human eye; the computer device 110 controls the refraction compensation module 109 to correct the refraction error (defocus, astigmatism, etc.) according to the measured wavefront aberration information, then the computer device 110 controls the distance of the sighting target image provided by the sighting target display 104 in front of the target human eye by controlling the driving mechanism 107 so that the target human eye 200 generates different diopter responses, and the Hartmann wavefront sensor 105 measures the responses of the human eye in the different diopter response states; visual function measurements, including but not limited to vision measurements of different distances, contrast sensitivity measurements, may be made by the subject's eyes observing measurement tasks on the optotype display 104.
Referring to fig. 1 and 2, the computer device 110 can calculate out defocus, astigmatism axis and other information according to the wavefront aberration information measured by the hartmann wavefront sensor 105, and the computer device 110 controls the refraction compensation module 109 to correct the corresponding ametropia, so that monocular objective aberration measurement and ametropia correction are completed.
In the objective aberration measurement process, if binocular synchronous measurement is to be performed, alignment of both eyes is performed first, and then synchronous measurement of wavefront aberrations of both eyes is completed under the condition of fixation of both eyes.
The human eye measurement device 100 of the present disclosure can realize the measurement of wavefront aberration of a target human eye in different diopter response states:
referring to fig. 1, after objective aberration measurement and ametropia correction are completed, the computer device 110 controls the driving mechanism 107 to drive the optotype display 104 to move to different positions in front of the target human eye to generate different diopter stimuli, and the hartmann wavefront sensor 105 measures the aberration of the human eye in different diopter response states, so that aberration measurement in different diopter response states can be completed, and diopter adjustment response amounts of the human eye are obtained.
Referring to fig. 1, vision measurements in a variety of measurement states may be made, illustratively, based on the human eye measurement device of the present disclosure:
(1) The computer device 110 controls the driving mechanism 107 of the two monocular measurement modules to enable the optotype display 104 to move to a position 30cm in front of the target human eyes, wavefront aberration measurement and ametropia correction of the left eye and the right eye are respectively carried out at the current positions, the computer device 110 controls the test tasks displayed by the optotype display 104, and myopia measurement of the left eye and myopia measurement of the right eye are respectively completed.
(2) The computer device 110 controls the driving mechanism 107 of the two monocular measurement modules to enable the optotype display 104 to move to the position 60cm in front of the target human eyes, wavefront aberration measurement and ametropia correction of the left eye and the right eye are respectively carried out at the current positions, the computer device 110 controls the test tasks displayed by the optotype display 104, and middle vision measurement of the left eye and middle vision measurement of the right eye are respectively completed.
(3) The computer device 110 controls the driving mechanism 107 of the two monocular measurement modules to enable the optotype display 104 to move to the position 500cm in front of the target human eyes, the wavefront aberration measurement and the ametropia correction of the left eye and the right eye are respectively carried out at the current positions, the computer device 110 controls the test tasks displayed by the optotype display 104, and the far vision measurement of the left eye and the far vision measurement of the right eye are respectively completed.
(4) Firstly, binocular alignment is completed, then the computer equipment 110 controls the left and right sighting target displays 104 to display the same test task, the computer equipment 110 controls the driving mechanism 107 to enable the sighting target displays 104 to respectively move to the positions 30mm, 60mm and 500cm in front of the measuring eyes, wavefront aberration measurement and ametropia correction of the left and right eyes are respectively carried out at the current positions, and binocular near vision, binocular middle vision and binocular far vision measurement are completed under binocular fusion conditions.
Referring to fig. 2, the above measurement may also be performed by the human eye measurement device shown in fig. 2, and will not be described again.
Taking fig. 1 as an example, the human eye measurement device of the present disclosure is capable of performing contrast sensitivity measurement, which may be based on the following steps:
(1) The computer device 110 controls the driving mechanism 107 to move the optotype display 9 to a position 500cm in front of the measuring eye (namely, the target human eye), the wavefront aberration measurement and the ametropia correction of the left eye are carried out at the current position, the computer device 110 controls the left-path optotype display 104 to randomly generate grating stripes with different spatial frequencies and different contrast values according to a contrast sensitivity measurement method, and a tested person answers according to subjective energy recognition to obtain a contrast sensitivity measurement result of the left eye.
(2) The computer device 110 controls the driving mechanism 107 to move the optotype display 9 to a position 500cm in front of the measuring eye (namely, the target human eye), the wavefront aberration measurement and the ametropia correction of the right eye are carried out at the current position, the computer device 110 controls the right-path optotype display 104 to randomly generate grating stripes with different spatial frequencies and different contrast values according to a contrast sensitivity measurement method, and a tested person answers according to subjective energy recognition to obtain a contrast sensitivity measurement result of the right eye.
(3) The computer device 110 controls the driving mechanism 107 to enable the two sighting target displays 104 to respectively move to the position 500cm in front of the measuring eyes, binocular alignment is firstly completed, wavefront aberration measurement and ametropia correction of the eyes are carried out at the current position, then the computer device 110 controls the left sighting target display 104 and the right sighting target display 104 to display the same target, namely, grating stripes with different spatial frequencies and different contrast values are randomly displayed, a tested person answers according to subjective energy recognition, and a contrast sensitivity measuring result of the eyes is obtained.
Contrast sensitivity measurements in different diopter response states can be accomplished by the computer device 110 controlling the drive mechanism 107 to move the optotype display 9 to different positions in front of the measuring eye (left and/or right eye).
Referring to fig. 2, the computer device 110 may also control the driving mechanism 107 to drive the focusing device 108 to complete the contrast sensitivity measurement under the condition of measuring the eye (left eye and/or right eye) and diopter response, which will not be described again.
In consideration of the defects of the existing aberration and vision function measuring device in the human eye adjusting state, the aberration measuring device can finish aberration measurement in the human eye adjusting state, vision measurement in short distance, middle distance and long distance and contrast sensitivity measurement of single/double eyes on the same instrument, under the condition that the measuring environment and the measuring condition are consistent, vision of human eyes in different adjusting reactions and different adjusting states is measured, and the measuring result can be used for effectively evaluating the vision functions of the human eyes/double eyes.
Based on the human eye measurement device of any one of the above embodiments provided by the present disclosure, the present disclosure further provides a human eye measurement method S100, referring to fig. 3, including:
s102, monocular or binocular wavefront aberration measurement is carried out, and wavefront aberration information is obtained;
s104, calculating and obtaining monocular or binocular refraction compensation amount based on the wavefront aberration information;
the method comprises the steps of enabling monocular or binocular to be in different diopter response states so as to conduct wave-front aberration information measurement, and further obtaining refraction compensation quantity of the monocular or binocular in the different diopter response states based on wave-front aberration information calculation.
In the description of the present specification, reference to the terms "one embodiment/manner," "some embodiments/manner," "example," "a particular example," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment/manner or example is included in at least one embodiment/manner or example of the present disclosure. In this specification, the schematic representations of the above terms are not necessarily for the same embodiment/manner or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments/modes or examples. Furthermore, the various embodiments/modes or examples described in this specification and the features of the various embodiments/modes or examples can be combined and combined by persons skilled in the art without contradiction.
Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present disclosure, the meaning of "a plurality" is at least two, such as two, three, etc., unless explicitly specified otherwise.
It will be appreciated by those skilled in the art that the above-described embodiments are merely for clarity of illustration of the disclosure, and are not intended to limit the scope of the disclosure. Other variations or modifications will be apparent to persons skilled in the art from the foregoing disclosure, and such variations or modifications are intended to be within the scope of the present disclosure.
Claims (10)
1. A human eye measurement device comprising a monocular measurement module, the monocular measurement module comprising:
a beacon light source for emitting an initial light;
a first parallel light conversion device that converts the initial light into parallel light;
the light path adjusting component is used for adjusting the light path of the parallel light output by the first parallel light conversion device so as to irradiate the target human eyes;
a optotype display providing an optotype image with a distance from the target human eye that can be adjusted to cause the target human eye to produce different diopter responses; and
a Hartmann wavefront sensor for receiving retinal reflected light from the target human eye in different diopter response states for wavefront aberration information measurement;
when the distance between the sighting target image and the target human eye is adjusted, the optical path between the beacon light source and the target human eye is not adjusted.
2. The human eye measurement device according to claim 1, wherein the monocular measurement module further comprises:
and the optotype imaging objective lens is positioned between the optotype display and the target human eye so as to be beneficial to the target human eye to observe the optotype image.
3. The human eye measurement device according to claim 1 or 2, wherein the monocular measurement module further comprises:
the driving mechanism can adjust the position of the sighting target display to adjust the distance between the sighting target image provided by the sighting target display and the target human eye.
4. The human eye measurement device according to claim 1 or 2, wherein the monocular measurement module further comprises:
a focusing device for adjusting a distance between a target image provided by the target display and the target human eye by changing a position; and
and a driving mechanism capable of driving the focusing device to cause the focusing device to change position.
5. The human eye measurement device according to claim 4, wherein the focusing device comprises a single lens, a transmissive/reflective lens group, or a variable focus liquid lens.
6. The human eye measurement device according to claim 3 or 4, wherein the driving mechanism comprises a motor and a transmission mechanism driven by the motor, so that the driving action of the driving mechanism is outputted through the transmission mechanism.
7. The human eye measurement device according to claim 1, wherein the monocular measurement module further comprises:
the refraction compensation module is configured in front of the target human eye to perform refraction compensation when the target human eye observes the sighting target image.
8. The human eye measurement device of claim 7, wherein the retinal reflected light from the target human eye in different diopter response states is received by the hartmann wavefront sensor via the refraction compensation module, an optical path adjustment assembly in sequence for wavefront aberration information measurement.
9. The human eye measurement device according to any one of claims 1 to 8, further comprising:
a computer device capable of controlling a refractive compensation amount of a refractive compensation module based on wavefront aberration information measured by the hartmann wavefront sensor;
optionally, the refraction compensation module can perform refraction compensation when the target human eye in different refraction response states observes the optotype image;
optionally, the refraction compensation module comprises a transmissive/reflective 4f system in combination with a cylindrical lens group, a liquid lens, a flexible zoom lens, a anamorphic mirror, or a liquid crystal spatial light modulator;
optionally, the human eye measuring device is a monocular measuring device or a binocular measuring device, when the human eye measuring device is a binocular measuring device, the two monocular measuring devices are symmetrically arranged so as to be capable of binocular measurement;
alternatively, both of the monocular measurement modules perform information processing and control based on the same computer device.
10. A method of measuring a human eye, comprising:
monocular or binocular wavefront aberration measurement is carried out to obtain wavefront aberration information; and
calculating and obtaining a monocular or binocular refraction compensation amount based on the wavefront aberration information;
wherein the wavefront aberration information measurement is made with monocular or binocular in different diopter response states;
optionally, the method further comprises:
and calculating and obtaining the refraction compensation quantity of the monocular or binocular in different diopter response states based on the wavefront aberration information.
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN118266857A (en) * | 2024-05-31 | 2024-07-02 | 瑞尔明康(浙江)医疗科技有限公司 | Human eye measuring system |
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| CN110367924A (en) * | 2019-08-22 | 2019-10-25 | 长兴爱之瞳医疗科技有限公司 | A kind of accurate optometry equipment of subjective and objective integral type and optometry method |
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| CN107788946A (en) * | 2016-09-05 | 2018-03-13 | 尼德克株式会社 | Subjective formula optometry equipment and subjective formula optometry program |
| CN110367924A (en) * | 2019-08-22 | 2019-10-25 | 长兴爱之瞳医疗科技有限公司 | A kind of accurate optometry equipment of subjective and objective integral type and optometry method |
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