Ophthalmic devices and ophthalmic systems

Abstract

Provided are an ophthalmic device that can be used in conjunction with an existing corrective device as needed and an ophthalmic system having the ophthalmic device. The ophthalmic device is connected to a corrective device that corrects the visual function of an eye to be inspected, the corrective device having two inspection windows arranged along an optical axis in pairs on the left and right and an arrangement mechanism for arranging one or more first optical elements between the two inspection windows, the ophthalmic device comprising: a connecting member that is detachably connected to the connected member using a member provided on the side of the corrective device on the side opposite to the eyepiece side of the eye to be inspected as the connected member; a second optical element that, when the connecting member is connected to the connected member, is arranged at a position opposite to the second inspection window on the side opposite to the first inspection window for the eyepiece of the eye to be inspected among the two inspection windows, the second optical element causing a second optical path to branch from the first optical path along the optical axis; and an objective measurement system that is arranged on the second optical path and acquires the ocular characteristics of the eye to be inspected.

Description

Technical Field

[0001] The present invention relates to an ophthalmologic apparatus for acquiring ocular characteristics of an eye to be examined, and an ophthalmologic system including the ophthalmologic apparatus. Background Art

[0002] In ophthalmology and optical shops, in order to conduct a subjective examination of the visual functions such as the vision of the eye to be examined, an optotype presentation device and a pair of left and right phoroptors (correction devices) are provided (refer to patent document 1). The optotype presentation device presents an optotype chart such as the Rondo ring optotype to the eye to be examined. In each phoroptor, an inspection window is formed, and a lens disk with a plurality of trial lenses of different degrees is stored so as to be rotatable. Each phoroptor arranges one or more trial lenses at a position corresponding to the inspection window by rotating the lens disk. In the subjective examination of the vision of the eye to be examined, the subject observes the optotype chart presented by the optotype presentation device through one or both of the left and right inspection windows, while answering questions from the examiner.

[0003] In each phoropter, the type (power) of the trial lens initially arranged at the position corresponding to the inspection window is determined based on the measurement results of an ophthalmic device such as a wavefront sensor that objectively measures the ocular characteristics such as the refractive power of the eye to be inspected (see Patent Documents 2 and 3). The ophthalmic device can be integrated with each phoropter as described in Patent Document 4, for example.

[0004] Prior Art Literature

[0005] Patent Literature

[0006] Patent Document 1: Japanese Patent Application Publication No. 2001-346762

[0007] Patent Document 2: Japanese Patent Application Publication No. 2017-169601

[0008] Patent Document 3: Japanese Patent Application Publication No. 2014-30573

[0009] Patent Document 4: U.S. Patent No. 9462939 Summary of the invention

[0010] Problems to be solved by the invention

[0011] However, when the ophthalmic device for objective measurement is not integrated with each comprehensive ophthalmometer, the examiner needs to input the measurement result of the ophthalmic device to the controller of each comprehensive ophthalmometer, and the measurement result cannot be directly input from the ophthalmic device to the controller. In addition, in this case, the ophthalmic device cannot measure the eye characteristics of the subject's eye that is observing the sight chart through the inspection window in real time and continuously, and the measurement result cannot be fed back to each comprehensive ophthalmometer (controller).

[0012] On the other hand, when a comprehensive ophthalmometer system is used that integrates an ophthalmic device with each comprehensive ophthalmometer as described in Patent Document 4, even if the above-mentioned problems can be solved, it is necessary to replace the existing comprehensive ophthalmometer with the comprehensive ophthalmometer system or to introduce the comprehensive ophthalmometer system separately, which is not realistic from the perspective of cost. In addition, there are differences in needs for each user, such as whether an ophthalmic device is needed or not, but the ophthalmic device cannot be omitted in the comprehensive ophthalmometer system described in Patent Document 4, so it is impossible to meet the needs of users who do not need an ophthalmic device.

[0013] The present invention has been made in view of the above circumstances, and an object of the present invention is to provide an ophthalmologic device that can be used integrally with an existing corrective device as needed, and an ophthalmologic system including the ophthalmologic device.

[0014] Solutions to Solve Problems

[0015] An ophthalmic device for achieving the purpose of the present invention is connected to a corrective device for correcting the visual function of an eye to be inspected, the corrective device having two inspection windows arranged in pairs along an optical axis on the left and right, and a configuration mechanism for configuring one or more first optical elements between the two inspection windows, wherein the ophthalmic device comprises: a connecting member, which is connected to the connected member in a removable manner using a member provided on the side of the corrective device on the opposite side of the eyepiece side of the eye to be inspected as the connected member; a second optical element, which is arranged at a position opposite to the second inspection window when the connecting member is connected to the connected member, the second inspection window being the inspection window on the opposite side of the first inspection window for the eyepiece of the eye to be inspected among the two inspection windows, the second optical element causing a second optical path to branch from the first optical path along the optical axis; and an objective measurement system, which is arranged on the second optical path to obtain eye characteristics of the eye to be inspected.

[0016] This ophthalmic device can be detachably connected to a connected member of a correction device, and thus can be used integrally with an existing correction device as needed.

[0017] In the ophthalmologic apparatus according to another aspect of the present invention, the connecting member is detachably connected to the second inspection window as the connected member.

[0018] The ophthalmic device of another embodiment of the present invention includes a housing for storing a second optical element and an objective measurement system, and when a back cover forming a side surface of the correction device on which a second inspection window is provided is removed from the correction device and a connecting member is connected to the second inspection window, the housing becomes a substitute for the back cover. Thus, the housing of the ophthalmic device can be used as a back cover of the correction device.

[0019] In an ophthalmic device of another embodiment of the present invention, a second optical element on the left and right sides of the optical axis is arranged on the optical axis for each of the left and right optical axes, so that the second optical path branches from the first optical path in directions parallel to and away from the two surfaces including the optical axis. Thus, when the eyes of the subject are converging, interference between the left and right ophthalmic devices is prevented.

[0020] An ophthalmic device according to another embodiment of the present invention includes an output unit that outputs the result of the eye characteristic obtained by the objective measurement system to a drive control unit that controls the drive of the configuration mechanism. Thus, the result of the eye characteristic obtained by the objective measurement system can be fed back to the correction device to quickly change the first optical element configured on the optical axis.

[0021] An ophthalmic device according to another embodiment of the present invention includes an observation system that obtains an observation image of the anterior ocular segment of a subject's eye, and an alignment detection unit that detects the relative positional relationship between the subject's eye and the ophthalmic device based on the observation image obtained by the observation system. Thus, alignment detection of the ophthalmic device relative to the subject's eye can be automatically performed.

[0022] An ophthalmic device according to another embodiment of the present invention includes an alignment control unit, which is connected to a relative movement mechanism that moves one of the eye to be inspected and the correction device relative to the other, and drives the relative movement mechanism based on the detection result of the alignment detection unit to align the ophthalmic device with respect to the eye to be inspected. Thus, the ophthalmic device can be automatically aligned with respect to the eye to be inspected.

[0023] An ophthalmic system for achieving the purpose of the present invention comprises: a correction device that corrects the visual function of the eye to be examined and comprises two inspection windows arranged in pairs along the optical axis on the left and right, and a configuration mechanism for configuring one or more first optical elements between the two inspection windows; and the above-mentioned ophthalmic device.

[0024] Effects of the Invention

[0025] The present invention can integrate the ophthalmic device with the existing corrective device as needed. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 This is a three-dimensional diagram of the appearance of the ophthalmic system.

[0027] Figure 2 This is a front view when observing the left and right comprehensive ophthalmometers from the side opposite to the sight mark presenting device, that is, the side opposite to the side opposite to the subject.

[0028] Figure 3 It is a cross-sectional view of the left and right phoropter connected with the wavefront sensor.

[0029] Figure 4It is a cross-sectional view of the left and right phoropter before connecting the wavefront sensor.

[0030] Figure 5 This is a schematic diagram of the optical system of the wavefront sensor corresponding to the right eye of the subject.

[0031] Figure 6 It is the functional block diagram of the controller.

[0032] Figure 7 This is a flowchart showing the flow of a process of determining a prescription value of a subject's spectacle lenses using an ophthalmologic system.

[0033] Figure 8 This is a functional block diagram of a controller constituting the ophthalmologic system according to the second embodiment.

[0034] Fig. 9 It is a cross-sectional view of a phoropter and a wavefront sensor constituting the ophthalmologic system according to the third embodiment, and is a cross-sectional view showing a state before the wavefront sensor and the phoropter are connected.

[0035] Fig.10 1 is a cross-sectional view of a phoropter and a wavefront sensor constituting the ophthalmologic system according to the third embodiment, and is a cross-sectional view showing a state in which the wavefront sensor and the phoropter are connected.

[0036] Fig.11 This is a schematic diagram of an optical system of a wavefront sensor according to another embodiment corresponding to the right eye of the subject. DETAILED DESCRIPTION

[0037] [First embodiment]

[0038] <Structure of the ophthalmology system>

[0039] Figure 1 is a perspective view of the appearance of the ophthalmic system 9. Figure 1 As shown, the ophthalmological system 9 is used, for example, to determine the prescription value of the power of the eyeglass lenses or the like worn by the subject H1. The ophthalmological system 9 includes a sight mark presenting device 10, a controller 11, an ophthalmological stand 12, and a pair of left and right phoroptors 14. In addition, the ophthalmological system 9 includes a pair of left and right wavefront sensors 20 (see FIG. 1 ) for objectively measuring the ocular characteristics of the subject's eye E. Figure 2 ).

[0040] The sight mark presenting device 10 is applied to the eye E of the subject H1 (refer to Figure 3) is a subjective examination of visual functions such as vision. The sight mark presenting device 10 is fixed on the side opposite to the subject H1 with the ophthalmoscope table 12 as a reference. It should be noted that the sight mark presenting device 10 can also be configured on the ophthalmoscope table 12. Under the control of the controller 11, the sight mark presenting device 10 presents various sight mark charts 13 to the subject's eye E through the display window 10a. It should be noted that the structure of the sight mark presenting device 10 is a well-known technology, so the specific description is omitted here.

[0041] The ophthalmometer 12 is disposed between the subject H1 and the sight mark presenting device 10. The ophthalmometer 12 can be raised and lowered freely in the vertical direction, and the height position in the vertical direction is adjusted according to the body shape of the subject H1. Thus, the subject H1 can place his elbow on the upper surface of the ophthalmometer 12 to stabilize his posture. In addition, the controller 11 is disposed on the upper surface of the ophthalmometer 12, and a rod 16 is fixed.

[0042] An arm 18 extending in the lateral direction is provided on the upper portion of the rod 16 , and a pair of left and right phoroptors 14 (also referred to as refractor heads) are suspended and fixed at the front end of the arm 18 .

[0043] A pair of left and right comprehensive ophthalmometers 14 is equivalent to the correction device of the present invention, and is connected to the eye E to be examined (refer to Figure 3 ) are respectively set correspondingly to the eyes of the respective holistic ophthalmometers 14. Under the control of the controller 11, each comprehensive ophthalmometer 14 puts the trial lens 24b (reference Figure 3 ) is appropriately arranged in front of the subject's eye E to correct the visual function of the subject's eye E. The subject H1 looks through the inspection windows 22, 23 of one or both of the left and right phoropter 14 (see Figure 3 ) to observe the sight chart 13 while answering questions from the examiner H2.

[0044] The controller 11 receives an input operation from the examiner H2 and controls the driving of the optotype presenting device 10 , each phoropter 14 , and each wavefront sensor 20 based on the input operation.

[0045] Figure 2 This is a front view of the left and right phoropter 14 when viewed from the side opposite to the sight mark presenting device 10, that is, the side opposite to the side opposite to the subject H1. Figure 2 As shown, in each comprehensive ophthalmometer 14, the first inspection window 22 (refer to Figure 3 ) are independently and detachably connected to the second inspection windows 23 on the opposite side of the eye E. Therefore, when only the subjective inspection of the visual acuity of the eye E is performed, each wavefront sensor 20 is removed from each phoropter 14 (see Figure 2On the other hand, when the subjective examination is performed using the objective measurement results of the eye characteristics of the subject's eye E, a wavefront sensor 20 (see FIG. Figure 2 2B). It should be noted that, it is also possible to perform only subjective inspection in a state where each phoropter 14 is connected to a wavefront sensor 20.

[0046] <Comprehensive ophthalmometer>

[0047] Figure 3 It is a cross-sectional view of the left and right phoropter 14 to which the wavefront sensor 20 is connected. Figure 4 FIG. 2 is a cross-sectional view of the left and right phoropter 14 before the wavefront sensor 20 is connected. Figure 3 and Figure 4 As shown, each comprehensive ophthalmometer 14 has the same structure as the existing device, and has an optical axis OA, a first inspection window 22 and a second inspection window 23 arranged along the optical axis OA, a rotating disk mechanism 24, and a comprehensive ophthalmometer housing 25. It should be noted that each comprehensive ophthalmometer 14 has a bilaterally symmetrical structure, so the structure of one side of each comprehensive ophthalmometer 14 is described here.

[0048] The optical axis OA is the optical axis of the first inspection window 22 , the second inspection window 23 , and the optical element, and is parallel to the front-rear direction (working distance direction) from the subject H1 toward the optotype presenting device 10 .

[0049] The first inspection window 22 and the second inspection window 23 are equivalent to the two inspection windows of the present invention, and are arranged at intervals along the optical axis OA. The first inspection window 22 is an inspection window for the eyepiece of the subject's eye E, and is arranged on the front side of the comprehensive ophthalmometer housing 25 on the side opposite to the subject's eye E. In addition, the second inspection window 23 is arranged on the rear side of the comprehensive ophthalmometer housing 25 on the side opposite to the side opposite to the subject's eye E (the side opposite to the sight mark presenting device 10). The second inspection window 23 (opening 23a, refer to Figure 4 ) functions as the connected structure of the present invention. It should be noted that Figure 2 and Figure 3 In the embodiment, transparent plates are cited as examples of the inspection windows 22 and 23 , but the inspection windows 22 and 23 may be opening holes.

[0050] The rotating disk mechanism 24 corresponds to the configuration mechanism of the present invention and is housed in the comprehensive ophthalmometer housing 25. The rotating disk mechanism 24 includes a plurality of lens disks 24a and a motor drive mechanism (not shown). Each lens disk 24a is formed in a disk shape. In addition, each lens disk 24a is rotatably held by a rotating shaft (not shown) extending in a direction parallel to the optical axis OA (front-rear direction).

[0051] A plurality of trial lenses 24b (equivalent to the first optical element of the present invention) with different degrees and at least one opening hole (not shown) are arranged along the circumference of each lens disk 24a. It should be noted that the first optical element of the present invention is not limited to the trial lens 24b, and includes, for example, various optical elements such as a pinhole, a Maddox lens, a red and green filter, a shielding plate, a cross cylindrical lens, and a polarizing plate. Each lens disk 24a rotates around a rotation axis (not shown) as the center, thereby selectively arranging any one of the plurality of trial lenses 24b or an opening hole on the optical axis OA.

[0052] The motor drive mechanism (not shown) rotates each lens disk 24a around the aforementioned rotation axis (not shown) under the control of the controller 11. Thus, one or more trial lenses 24b are arranged between the first inspection window 22 and the second inspection window 23. It should be noted that the motor drive mechanism is a known technology (for example, refer to Patent Document 1), and thus a detailed description thereof is omitted.

[0053] <Wavefront Sensor>

[0054] The left and right wavefront sensors 20 constitute the ophthalmic device of the present invention together with the controller 11 described above. Each wavefront sensor 20 includes a sensor housing 26, a dichroic mirror 28, and a wavefront sensor body 29. It should be noted that each wavefront sensor 20 has a left-right symmetrical structure, so the structure of one of the wavefront sensors 20 will be described here.

[0055] The sensor housing 26 holds the dichroic mirror 28 and accommodates the wavefront sensor body 29. In addition, a cylindrical connecting member 27 is provided on the front side surface of the sensor housing 26 on the side facing the phoropter 14. In addition, the dichroic mirror 28 is held in a tilted state relative to the optical axis OA on the rear side surface of the sensor housing 26 on the side facing the sight mark presenting device 10.

[0056] The connecting member 27 has a shape that can be detachably connected to the opening 23a of the second inspection window 23 of the phoropter 14 by, for example, a metal material or a hard resin material. It should be noted that the connecting member 27 may be formed integrally with the sensor housing 26, or the connecting member 27 formed separately from the sensor housing 26 may be fixed or connected (connected) to the sensor housing 26. By connecting (fitting) the connecting member 27 to the opening 23a, the wavefront sensor 20 is connected and held to the phoropter 14.

[0057] An infrared light source 99 is provided inside the connecting member 27 at a position that does not hinder the subject's eye E from visually observing the sight chart 13 and does not hinder measurement by a wavefront sensor main body 29 described later (see Figure 5The infrared light source 99 emits near infrared light LA ​​(see FIG. 1 ) toward the eye E to be examined via the inspection windows 22 and 23 of the comprehensive ophthalmometer 14 and the trial lens 24b. Figure 5 The wavelength range of the near infrared light LA ​​is, for example, 940 to 950 nm. It should be noted that the infrared light source 99 may be provided between the connecting member 27 and the dichroic mirror 28 inside the sensor housing 26 instead of being provided inside the connecting member 27 .

[0058] The dichroic mirror 28 is equivalent to the second optical element of the present invention. The dichroic mirror 28 is held by the rear side of the sensor housing 26 at a position opposite to the connecting member 27 in a state inclined relative to the optical axis OA. When the connecting member 27 is connected to the opening 23a, the dichroic mirror 28 is arranged at a position opposite to the second inspection window 23 on the optical axis OA. Thus, the dichroic mirror 28 branches the second optical path LP2 from the first optical path LP1 along the optical axis OA.

[0059] A wavefront sensor main body 29 including an objective lens 30 is provided on the second optical path LP2 branched by the dichroic mirror 28. Therefore, the sensor housing 26 has a shape extending in a direction parallel to the second optical path LP2.

[0060] Here, the branching direction of the second optical path LP2 based on the left and right dichroic mirrors 28 is set to be parallel to the plane (horizontal plane) including both sides of the left and right optical axes OA and to be away from each other in the outer direction. In other words, the left and right wavefront sensors 20 are connected to the left and right phoropter 14 in such a manner that the branching directions of the second optical path LP2 based on the left and right dichroic mirrors 28 are directed outwards. Thus, the dichroic mirror 28 disposed on the optical axis OA on the left eye side branches the second optical path LP2 from the optical axis OA to the left direction. In addition, the dichroic mirror 28 disposed on the optical axis OA on the right eye side branches the second optical path LP2 from the optical axis OA to the right direction.

[0061] If the branching direction of the second optical path LP2 based on each dichroic mirror 28 is set to the upward direction or the downward direction, when the two phoroptors 14 are aligned with respect to the eyes of the subject's eye E in a state of convergence, the left and right wavefront sensors 20 may interfere with each other. In contrast, in the present embodiment, the branching directions of the second optical path LP2 based on the left and right dichroic mirrors 28 are set to face outwards from each other, thereby reliably preventing the left and right wavefront sensors 20 from interfering with each other.

[0062] It should be noted that in the present embodiment, on the horizontal plane described above, the second light path LP2 is perpendicular (including substantially perpendicular) to the first light path LP1 , but the second light path LP2 may be inclined relative to the first light path LP1 .

[0063] In addition, the dichroic mirror 28 of the present embodiment is provided with a compensating optical element 48 (AO: Adaptive Optics). It should be noted that the compensating optical element 48 may not be provided.

[0064] Figure 5 2 is a schematic diagram of the optical system of the wavefront sensor 20 (dichroic mirror 28 and wavefront sensor main body 29) corresponding to the right eye of the subject's eye E. It should be noted that the optical systems of the left and right wavefront sensors 20 are bilaterally symmetrical, so the structure of the optical system of the wavefront sensor 20 corresponding to the right eye of the subject's eye E will be described here. Figure 5 In order to avoid complication of the drawing, the phoropter 14, the dichroic mirror 28, and the wavefront sensor body 29 are shown separately.

[0065] like Figure 5 As shown, the dichroic mirror 28 transmits visible light (wavelength range: about 380nm to 780nm) and reflects near-infrared light (wavelength range: about 800nm ​​to 1100nm) having a wavelength range different from that of the visible light. Specifically, the dichroic mirror 28 reflects the near-infrared light LB incident from the wavefront sensor body 29 described later toward the eye to be examined E. In addition, the dichroic mirror 28 reflects the near-infrared light LA ​​and LB incident from the eye to be examined E through the inspection windows 22 and 23 of the comprehensive ophthalmometer 14 toward the wavefront sensor body 29. It should be noted that the image light of the sight chart 13 passes through the dichroic mirror 28, so the eye to be examined E can visually observe the sight chart 13.

[0066] The wavefront sensor body 29 is a measuring machine capable of continuously performing measurements, and is used to measure the ocular characteristics (wavefront aberration) of the subject's eye E. In addition, the wavefront sensor body 29 is also used to measure the eye position (line of sight direction) of the subject's eye E, the convergence angle of the subject's eye E, and the observation of the anterior ocular part (detection of pupil diameter and pupil center). The wavefront sensor body 29 emits near-infrared light LB toward the dichroic mirror 28, receives near-infrared light LA ​​and LB of two wavelengths reflected by the dichroic mirror 28, and outputs a light reception signal of each wavelength region to the controller 11.

[0067] The wavefront sensor main body 29 includes an anterior ocular segment observation system 29A, an aberration measurement system 29B, an objective lens 30 , a dichroic mirror 31 , and a reflecting mirror 32 .

[0068] The objective lens 30 emits the near infrared light LB of a wavelength of 830 to 840 nm incident from the aberration measuring system 29B described later via the reflection mirror 32 and the dichroic mirror 31 toward the dichroic mirror 28. In addition, the near infrared light LA ​​and LB of two wavelengths reflected by the eye E are incident on the objective lens 30 via the first optical path LP1, the dichroic mirror 28, and the second optical path LP2. The near infrared light LA ​​and LB pass through the objective lens 30 and are incident on the dichroic mirror 31.

[0069] The dichroic mirror 31 transmits near infrared light LA ​​having a wavelength of 940 to 950 nm, and reflects near infrared light LB having a wavelength of 830 to 840 nm. Thus, the dichroic mirror 31 reflects the near infrared light LB incident from the aberration measuring system 29B described later via the reflector 32 toward the objective lens 30. In addition, the dichroic mirror 31 allows the near infrared light LA ​​of the two wavelengths of near infrared light LA ​​and LB incident from the objective lens 30 to be incident on the anterior ocular observation system 29A, and reflects the near infrared light LB toward the reflector 32.

[0070] The reflection mirror 32 reflects the near-infrared light LB incident from either the aberration measuring system 29B or the dichroic mirror 31 toward the other.

[0071] The anterior ocular segment observation system 29A corresponds to the observation system of the present invention, and receives the near-infrared light LA ​​under the control of the controller 11 to obtain an observation image of the subject's eye E. The observation image is used, for example, for alignment, the eye position (line of sight direction) of both eyes of the subject's eye E, the convergence state, and the measurement (including detection, detection, inspection, and judgment) of the pupil diameter. The anterior ocular segment observation system 29A includes an alignment optical system 34, relay lenses 35A and 35B, an imaging lens 36, and an imaging element 37 (light receiving element).

[0072] The alignment optical system 34 projects an alignment light beam to the anterior segment of the subject's eye E via the dichroic mirror 31, the objective lens 30, and the dichroic mirror 28. As a result, a bright spot image is generated in the observation image of the anterior segment obtained by the imaging element 37 described later, so that the wavefront sensor 20 can be aligned with respect to the subject's eye E. It should be noted that in the first embodiment, the alignment is performed manually by the examiner H2.

[0073] The relay lenses 35A and 35B emit the near infrared light LA ​​incident from the dichroic mirror 31 toward the imaging lens 36. The imaging lens 36 forms an image on the light receiving surface of the imaging element 37 of the near infrared light LA ​​(anterior ocular image light) incident from the relay lens 35B.

[0074] The imaging element 37 is a well-known area sensor (area image sensor), receives (images) the near-infrared light LA ​​formed by the imaging lens 36 , and outputs a light reception signal representing an observed image of the anterior ocular segment of the subject's eye E to the controller 11 .

[0075] The aberration measuring system 29B constitutes a part of the objective measuring system of the present invention, and receives near-infrared light LB under the control of the controller 11, and outputs a light receiving signal for measuring the eye refractive power and the like of the subject's eye E. The aberration measuring system 29B includes a semiconductor light source 40 such as an SLD (Super luminescent diode), a collimating lens 41, a polarizing beam splitter 42, a reflecting mirror 43, lens systems 44A and 44B, a Hartmann plate 45, and an imaging element 46 (light receiving element).

[0076] The semiconductor light source 40 emits near-infrared light LB with a wavelength of 830 to 840 nm toward the collimating lens 41. The collimating lens 41 converts the near-infrared light LB incident from the semiconductor light source 40 into approximately parallel light and then emits it toward the polarizing beam splitter 42. It should be noted that the semiconductor light source 40 is moved according to the degree of the eye E to be inspected as needed so that the near-infrared light LB is focused on the fundus of the eye E to be inspected.

[0077] The polarization beam splitter 42 reflects, for example, S polarized light and transmits P polarized light. The polarization beam splitter 42 reflects the near infrared light LB incident from the collimating lens 41 toward the reflector 32. Thus, the near infrared light LB is irradiated toward the subject's eye E via the reflector 32, the dichroic mirror 31, the objective lens 30, the dichroic mirror 28, the phoropter 14, and the like. Then, the near infrared light LB (return light) reflected by the subject's eye E travels in the opposite direction on the same path as the outgoing path and enters the polarization beam splitter 42.

[0078] The polarization beam splitter 42 transmits the near-infrared light LB incident from the reflection mirror 32 via the dichroic mirror 31 and the like as it is, and emits the near-infrared light LB toward the reflection mirror 43 .

[0079] The reflective mirror 43 reflects the near infrared light LB incident from the polarization beam splitter 42 toward the lens system 44A. The lens systems 44A and 44B emit the near infrared light LB incident from the reflective mirror 43 toward the Hartmann plate 45.

[0080] A plurality of micro lenses with equal focal lengths are formed on the surface of the Hartmann plate 45. The Hartmann plate 45 divides the near-infrared light LB incident from the lens system 44B into a plurality of light beams corresponding to the respective micro lenses, and images the respective light beams on the light receiving surface of the imaging element 46. It should be noted that the lens system 44B and the Hartmann plate 45 are moved as required so that substantially parallel light is incident from the lens system 44B to the Hartmann plate 45. In addition, the semiconductor light source 40, the lens system 44B, and the Hartmann plate 45 may be moved in conjunction with each other.

[0081] The imaging element 46 is a well-known area sensor, which receives (images) a plurality of light beams formed on the light receiving surface by the Hartmann plate 45, and outputs a light receiving signal representing a plurality of point images (Hartmann images) corresponding to each light beam to the controller 11. Thus, the wavefront aberration of the subject's eye E representing the eye characteristics (eye refractive power, etc.) of the subject's eye E can be measured.

[0082] The compensating optical element 48 (also called a wavefront compensation device) uses, for example, LCOS (Liquid Crystal On Silicon) or the like, but there is no particular limitation on its type. The compensating optical element 48 is controlled by the controller 11 to remove the high-order aberrations contained in the near-infrared light LB (return light) received by the shooting element 46 of the aberration measurement system 29B. It should be noted that the specific control method is a well-known technology, so the specific description is omitted here. In addition, in the present embodiment, the compensating optical element 48 is arranged on the dichroic mirror 28, but its configuration can be appropriately changed, and it can also be arranged between the sight mark presentation device 10 to enable the subject's eye E to be visible to the sight mark chart 13 when the high-order aberrations are removed.

[0083] <Controller>

[0084] Figure 6 is a functional block diagram of the controller 11. It should be noted that Figure 6 In the figure, the illustration of the sight mark presenting device 10 is omitted. Figure 6 As shown, the controller 11 and the wavefront sensor 20 together constitute a part of the ophthalmic device of the present invention. The controller 11 is connected to the sight mark presentation device 10, each comprehensive ophthalmometer 14 and each wavefront sensor 20 by wire or wirelessly, and uniformly controls the actions of these parts. It should be noted that the controller 11 of this embodiment is a controller that adds the function of controlling each wavefront sensor 20 (for example, added in the form of software) on the basis of the existing controller that controls the sight mark presentation device 10 and each comprehensive ophthalmometer 14 (refer to the above-mentioned patent document 1).

[0085] The controller 11 has a computing circuit composed of various processors and memories. The various processors include CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit) and programmable logic devices [such as SPLD (Simple Programmable Logic Devices), CPLD (Complex Programmable Logic Device) and FPGA (Field Programmable Gate Arrays)]. It should be noted that the various functions of the controller 11 can be implemented by one processor or by multiple processors of the same or different types.

[0086] The controller 11 functions as the phoropter control section 49 and the wavefront sensor control section 52 by reading and executing a program stored in a storage circuit or a storage device (not shown).

[0087] The phoropter control section 49 includes a power determination section 50 and a disk mechanism control section 51 .

[0088] When the wavefront sensor 20 is connected to each phoropter 14, the power determination unit 50 determines the power of the trial lens 24b for correcting the visual function of the subject's eye E based on the calculation result of the eye characteristic (wavefront aberration) of the subject's eye E input from the eye characteristic calculation unit 58 described later. The power includes, for example, spherical power (S: Sphere), cylindrical power (C: Cylinder), and astigmatism axis angle (A: AXIS).

[0089] For example, the power determination unit 50 determines the power of the trial lens 24b based on the second-order aberration of the wavefront aberration, or determines the power of the trial lens 24b based on the best focus, spot diameter and minimum RMS (Root Mean Square) wavefront aberration taking into account the higher-order aberration of the wavefront aberration. It should be noted that the method for determining the power of the trial lens 24b is a well-known technology, so the specific description is omitted.

[0090] In addition, when the wavefront sensor 20 is not connected to each comprehensive ophthalmometer 14, the degree determination unit 50 determines the degree of the trial lens 24b for correcting the visual function of the eye E to be examined based on the input information input by the examiner H2 to the controller 11, such as the measurement results of the eye characteristics (eye refractive power) of the eye E to be examined measured separately.

[0091] The disk mechanism control unit 51 constitutes a drive control unit of the present invention together with the power determination unit 50. The disk mechanism control unit 51 drives the rotary disk mechanism 24 based on the power of the trial piece 24b determined by the power determination unit 50 to arrange one or more trial pieces 24b on the optical axis OA.

[0092] The wavefront sensor control section 52 includes an observation system control section 54 , a measurement system control section 56 , an eye characteristic calculation section 58 , and a re-measurement control section 60 .

[0093] The observation system control unit 54 controls each part of the anterior ocular segment observation system 29A and the infrared light source 99, and executes the irradiation of the near-infrared light LA ​​by the infrared light source 99 to the subject's eye E, and the reception of the near-infrared light LA ​​(return light) by the imaging element 37. In addition, the observation system control unit 54 displays an observation image of the anterior ocular segment of the subject's eye E on a display unit (not shown) of the controller 11 based on a light reception signal of the near-infrared light LA ​​output from the imaging element 37.

[0094] The measurement system control unit 56 controls the aberration measurement system 29B and the compensation optical element 48, etc., and executes the irradiation of the subject's eye E with near-infrared light LB by the aberration measurement system 29B, the reception of the near-infrared light LB by the imaging element 46, and the removal of aberrations by the compensation optical element 48. The light reception signal of the near-infrared light LB output from the imaging element 46 is input to the eye characteristic calculation unit 58 described later.

[0095] The eye characteristic calculation unit 58 constitutes the objective measurement system of the present invention together with the aberration measurement system 29B described above. The eye characteristic calculation unit 58 calculates the eye characteristic (wavefront aberration) such as the eye diopter of the subject's eye E by a known method based on the light receiving signal of the near-infrared light LB input from the imaging element 46. Moreover, the eye characteristic calculation unit 58 functions as an output unit of the present invention after calculating the eye characteristic of the subject's eye E, and outputs the calculation result of the eye characteristic to the power determination unit 50. Thus, the power determination unit 50 automatically determines the power of the trial lens 24b, and the disk mechanism control unit 51 drives the rotating disk mechanism 24 (changes the trial lens 24b).

[0096] When the wavefront sensor 20 is connected to each phoropter 14 and the rotating disk mechanism 24 is driven, the re-measurement control unit 60 operates the measurement system control unit 56 and the eye characteristic calculation unit 58 again. As a result, the aberration measurement system 29B performs irradiation of the near-infrared light LB to the subject's eye E through the trial lens 24b and reception of the near-infrared light LB by the imaging element 46. In addition, the eye characteristic calculation unit 58 calculates the eye characteristics of the subject's eye E based on the light reception signal of the near-infrared light LB received by the imaging element 46.

[0097] Next, the re-measurement control unit 60 calculates the residual power by a known method based on the calculation result of the new eye characteristics of the subject's eye E by the eye characteristics calculation unit 58. Then, the re-measurement control unit 60 determines whether the residual power is within a prescribed range, for example, whether S and C are within ±0.25°. If the residual power is within the prescribed range, the re-measurement control unit 60 stops the operation.

[0098] On the other hand, when the residual power is out of the prescribed range, the re-measurement control unit 60 outputs the calculation result of the residual power to the power determination unit 50. Thus, the power determination unit 50 determines the power of the trial lens 24b re-arranged on the optical axis OA based on the power of one or more trial lenses 24b already arranged on the optical axis OA and the residual power, and outputs the determination result to the disk mechanism control unit 51. Then, the disk mechanism control unit 51 drives the rotating disk mechanism 24 to change the trial lens 24b arranged on the optical axis OA.

[0099] When the change of the trial lens 24b is completed, the re-measurement control unit 60 re-operates the measurement system control unit 56 and the eye characteristic calculation unit 58, and calculates and determines the residual diopter. Thereafter, the re-measurement control unit 60 repeatedly outputs the calculation result of the residual diopter to the diopter determination unit 50, re-operates the measurement system control unit 56 and the eye characteristic calculation unit 58, and calculates and determines the residual diopter until the residual diopter is within the specified range.

[0100] <Wavefront sensor alignment>

[0101] When the wavefront sensor 20 is connected to each phoropter 14, the optical axis OA of each phoropter 14 and the central axis of the connecting member 27 of the wavefront sensor 20 are aligned in the left-right direction (X direction) and the up-down direction (Y direction). In addition, if the wavefront sensor 20 is rotated around the axial circumference of the optical axis OA (Z axis), it affects the measurement result of the astigmatism degree of the eye E to be examined, so the rotation position of the wavefront sensor 20 is adjusted. For example, an astigmatic model eye is used for adjusting the rotation position.

[0102] [Function of the first embodiment]

[0103] Figure 7 1 is a flowchart showing the flow of a process for determining the prescription value of the eyeglass lenses of the subject H1 using the ophthalmologic system 9 having the above-described configuration. Figure 7 As shown, the examiner H2 first connects the connection member 27 of the wavefront sensor 20 to the opening 23 a of the second inspection window 23 of each phoropter 14 . Thus, the wavefront sensor 20 and each phoropter 14 are connected.

[0104] When the wavefront sensor 20 is started, the alignment optical system 34 irradiates the eye E with an alignment beam, the infrared light source 99 irradiates the eye E with near-infrared light LA, the anterior ocular segment observation system 29A obtains an observation image of the anterior ocular segment of the eye E, and a display unit (not shown) displays the observation image. The examiner H2 manually moves each phoropter 14 based on the observation image displayed on the display unit and the alignment beam in the observation image to perform manual alignment of each wavefront sensor 20 relative to the eye E (step SA1).

[0105] After the manual alignment is completed, when the examiner H2 inputs a measurement start instruction to the controller 11 (step SB1), the measurement system control unit 56 of the controller 11 outputs a control instruction to the aberration measurement system 29B and the compensation optical element 48 of the wavefront sensor 20, etc., to instruct them to operate (step SB2). As a result, the aberration measurement system 29B irradiates the subject's eye E with near-infrared light LB, the imaging element 46 receives the near-infrared light LB (step SC1), the compensation optical element 48 removes aberrations, and the imaging element 46 outputs a light reception signal to the eye characteristic calculation unit 58 of the controller 11 (step SC2).

[0106] The eye characteristic calculation unit 58, which receives the input of the light receiving signal from the imaging element 46, calculates the eye characteristic (wavefront aberration) such as the eye diopter of the subject's eye E based on the light receiving signal (step SB3). Thus, the eye characteristic of the subject's eye E observing the eye chart 13 through each inspection window 22, 23 can be measured in real time and continuously. Then, the eye characteristic calculation unit 58 outputs the calculation result of the eye characteristic of the subject's eye E to the diopter determination unit 50.

[0107] The power determination unit 50, which has received the calculation result of the eye characteristics from the eye characteristics calculation unit 58, determines the power (S, C, A) of the trial lens 24b based on the calculation result, and outputs the determination result to the disk mechanism control unit 51 (step SB4). Thus, the disk mechanism control unit 51 outputs a control command for instructing the placement of the trial lens 24b to the rotating disk mechanism 24 based on the power determined by the power determination unit 50 (step SB5). The rotating disk mechanism 24 receives the control command and drives, and places one or more trial lenses 24b on the optical axis OA (step SA2).

[0108] When the placement of the trial lens 24b is completed, the re-measurement control unit 60 operates the measurement system control unit 56 and the eye characteristic calculation unit 58 again. As a result, the measurement system control unit 56 outputs a control command to the aberration measurement system 29B and the compensation optical element 48 of the wavefront sensor 20 again (step SB6), and in response to the command, the imaging element 46 receives the near-infrared light LB (step SC3), and the imaging element 46 outputs a light receiving signal to the eye characteristic calculation unit 58 (step SC4).

[0109] Then, the eye characteristic calculation unit 58 calculates the eye characteristic (wavefront aberration) of the subject's eye E that has passed through the trial lens 24 b (step SB7 ). This allows the eye characteristic of the subject's eye E that has passed through the trial lens 24 b to be measured continuously and in real time.

[0110] Next, the re-measurement control unit 60 calculates the residual power based on the calculation result of the new eye characteristics of the subject's eye E performed by the eye characteristics calculation unit 58, and determines whether the residual power is within the specified range (step SB8). If the residual power is within the specified range, the process proceeds to step SB9 described later ("Yes" in step SB8).

[0111] On the other hand, when the residual power is out of the prescribed range ("No" in step SB8), the re-measurement control unit 60 outputs the calculation result of the residual power to the power determination unit 50. Thus, the power determination unit 50 determines the power of the trial lens 24b to be re-set on the optical axis OA based on the power of the trial lens 24b already set on the optical axis OA and the residual power (step SB4). Then, the processing of the steps SB5 and SA2 described above is repeated to change the trial lens 24b arranged on the optical axis OA. In this way, in this embodiment, the measurement result of the eye characteristics of the subject's eye E that has passed through the trial lens 24b can be quickly fed back to the comprehensive ophthalmometer 14, so that the trial lens 24b arranged on the optical axis OA can be quickly changed.

[0112] After the trial lens 24b is changed, the re-measurement control unit 60 operates the measurement system control unit 56 and the eye characteristic calculation unit 58 again. Thus, the processing of step SB6, step SC3, step SC4 and step SB7 described above is repeatedly executed. Then, the re-measurement control unit 60 determines whether the residual power is within the prescribed range (step SB8). Hereinafter, the above series of processing is repeated until the re-measurement control unit 60 determines that the residual power is within the prescribed range.

[0113] When the re-measurement control unit 60 determines that the residual diopter is within the predetermined range (YES in step SB8 ), the examiner H2 determines the prescription value of the diopter of the eyeglass lenses or the like worn by the subject H1 (step SB9 ).

[0114] [Effects of the First Embodiment]

[0115] As described above, in the ophthalmologic system 9 of the first embodiment, the wavefront sensor 20 can be detachably connected to the opening 23a of the second inspection window 23 of the existing phoropter 14, so the wavefront sensor 20 can be used integrally with the existing phoropter 14 as needed. As a result, the measurement result of the wavefront sensor 20 can be quickly fed back to the existing phoropter 14. In addition, by making it possible to connect the wavefront sensor 20 to the existing phoropter 14, the cost of the ophthalmologic system 9 can be suppressed. Furthermore, it is possible to meet the needs of both users who need the wavefront sensor 20 and users who do not need the wavefront sensor 20.

[0116] Furthermore, by connecting the wavefront sensor 20 to the existing phoropter 14, even when the subject's eye E is binocularly observing the sight chart 13, the aberration characteristics of both eyes (S, C, A and higher-order aberrations) can be measured, and the measurement can be performed in real time and continuously. Thus, the dynamic aberration characteristics of both eyes of the subject's eye E can be obtained.

[0117] [Second embodiment]

[0118] Figure 8 1 is a functional block diagram of the controller 11 constituting the ophthalmologic system 9 according to the second embodiment. In the first embodiment, the wavefront sensor 20 is manually aligned with respect to the left and right eyes E to be examined, but in the second embodiment, the alignment is automatically performed.

[0119] like Figure 8 As shown, the ophthalmologic system 9 of the second embodiment is configured as follows: a relative movement mechanism 66 is connected to the controller 11, and the wavefront sensor control unit 52 has the components described above (see Figure 6 ) and also functions as an alignment detection unit 62 and an alignment control unit 64, and is otherwise substantially the same as the ophthalmic system 9 of the first embodiment. Therefore, for portions that are the same in function or structure as those of the first embodiment, the same reference numerals are given and their descriptions are omitted.

[0120] The relative movement mechanism 66 is, for example, an actuator provided in at least one of the face support portion (chin rest) supporting the face of the subject H1, the ophthalmoscope table 12, the base end portion of the rod 16, the arm portion 18, etc., and moves the left and right phoroptors 14 relative to the subject's eye E in the up-down, left-right, front-back directions. Thus, each wavefront sensor 20 can be moved integrally with each phoroptor 14 in the up-down, left-right, front-back directions.

[0121] The alignment detection unit 62 performs alignment detection for detecting the relative positional relationship between the eye E and the wavefront sensor 20 for each of the left and right eyes E based on the observation image of the anterior segment of the eye E obtained by the anterior segment observation system 29A (including the image of the alignment light beam irradiated to the anterior segment by the alignment optical system 34). For example, the alignment detection unit 62 performs alignment detection of the wavefront sensor 20 in the up, down, left, and right directions relative to the eye E based on the position of the image of the alignment light beam in the observation image, and performs alignment detection of the wavefront sensor 20 in the front and back directions based on the focus state of the observation image. It should be noted that the specific alignment detection method is a well-known technology, so the description is omitted here. In addition, the alignment detection unit 62 outputs the alignment detection result to the alignment control unit 64.

[0122] The alignment control unit 64 drives the relative movement mechanism 66 based on the alignment detection result input from the alignment detection unit 62 to align the wavefront sensor 20 with respect to the left and right eyes E. Thus, automatic alignment of the wavefront sensor 20 with respect to the left and right eyes E can be performed.

[0123] [Third Embodiment]

[0124] Fig. 9 2 is a cross-sectional view of the phoropter 14 and the wavefront sensor 20 constituting the ophthalmologic system 9 of the third embodiment, and is a cross-sectional view showing a state before the wavefront sensor 20 and the phoropter 14 are connected. Fig.10 1 is a cross-sectional view of the phoropter 14 and the wavefront sensor 20 constituting the ophthalmologic system 9 of the third embodiment, and is a cross-sectional view showing a state where the wavefront sensor 20 is connected to the phoropter 14. It should be noted that since each phoropter 14 and each wavefront sensor 20 is a bilaterally symmetrical structure, Fig. 9 and Fig.10 In the description, the phoropter 14 and the wavefront sensor 20 corresponding to the right eye of the eye to be inspected E are taken as an example.

[0125] like Fig. 9 and Fig.10 As shown in the figure, in the third embodiment, when the wavefront sensor 20 is connected to the phoropter 14, the sensor housing 26 of the wavefront sensor 20 is used as the rear side surface of the phoropter housing 25 on the second inspection window 23 side. It should be noted that the third embodiment is basically the same structure as the above-mentioned embodiments except that the shapes of the phoropter housing 25 and the sensor housing 26 are partially different. Therefore, the same reference numerals are attached to the same parts as those of the above-mentioned embodiments in terms of function or structure, and their description is omitted.

[0126] The phoropter housing 25 of the third embodiment is detachably provided with a back cover 130 constituting the rear side surface on the second inspection window 23 side. The back cover 130 is removed from the phoropter housing 25 before the wavefront sensor 20 is connected to the phoropter 14 .

[0127] When the wavefront sensor 20 is connected to the phoropter 14 after the back cover 130 is removed from the phoropter housing 25, the sensor housing 26 of the third embodiment functions as a substitute for the back cover 130 by covering the housing opening 25a of the phoropter housing 25. Thus, the phoropter 14 and the wavefront sensor 20 can be integrated. As a result, the wavefront sensor 20 can be prevented from being displaced due to contact from the outside.

[0128] [Other embodiments of the wavefront sensor]

[0129] Fig.11 1 is a schematic diagram of an optical system of a wavefront sensor 100 of another embodiment corresponding to the right eye of the subject's eye E. It should be noted that since the optical systems of the left and right wavefront sensors 100 are bilaterally symmetrical, the structure of the optical system of the wavefront sensor 100 corresponding to the right eye of the subject's eye E is described here. In addition, for the same parts in function or structure as those in the above-mentioned embodiments, the same reference numerals are marked and their descriptions are omitted. And, Fig.11 The comprehensive ophthalmometer 14 in the figure is the same as the comprehensive ophthalmometer 14 described in the above embodiments, but in order to prevent the complication of the drawings, the illustration of part of the structure is omitted.

[0130] The wavefront sensor 100 includes a dichroic mirror 28 common to the above-mentioned embodiments and a wavefront sensor body 100a different from the above-mentioned embodiments. Fig.11 In the figure, the compensation optical element 48 provided in the dichroic mirror 28 is omitted from the illustration.

[0131] The sensor housing 125 of the wavefront sensor 100 holds the dichroic mirror 28 and accommodates the wavefront sensor body 100a. In addition, a connecting member 27A that can be detachably connected to the opening 23a of the second inspection window 23 of the phoropter 14 is formed in the sensor housing 125. The connecting member 27A is basically the same as the connecting member 27 of the above-mentioned embodiments. Thus, the wavefront sensor 100 can be detachably connected to the phoropter 14, similarly to the above-mentioned embodiments.

[0132] The dichroic mirror 28 (the second optical element of the present invention) is held at a position opposite to the connecting member 27A in a state inclined relative to the optical axis OA by the rear side of the sensor housing 125. When the connecting member 27A is connected to the opening 23a, the dichroic mirror 28 is arranged at a position opposite to the second inspection window 23 on the optical axis OA, thereby causing the second optical path LP2 to branch from the first optical path LP1 along the optical axis OA.

[0133] The dichroic mirror 28 transmits visible light and reflects near infrared light having a wavelength region different from that of the visible light, similarly to the first embodiment. Thus, the dichroic mirror 28 reflects the near infrared light LB incident from the wavefront sensor body 100a toward the subject's eye E. In addition, the dichroic mirror 28 reflects the near infrared light LA ​​and LB incident from the subject's eye E via the phoropter 14 toward the wavefront sensor body 100a.

[0134] The wavefront sensor body 100 a emits near-infrared light LB toward the dichroic mirror 28 , receives near-infrared light LA ​​and LB of two wavelengths reflected by the dichroic mirror 28 , and outputs a light reception signal for each wavelength region to the controller 11 .

[0135] The wavefront sensor body 100a includes an infrared light source 112, an objective lens 108, a dichroic mirror 107, an anterior ocular segment observation system G1, a light source system G2a and a light receiving system G2b constituting an aberration measurement system G2, an image data output unit 115, a mirror control unit 116, and an inclination angle detection unit 117. It should be noted that the infrared light source 112 and the inclination angle detection unit 117 may be omitted.

[0136] The infrared light source 112 is, for example, an LED (Light Emission Diode) that emits infrared light (near infrared light LA) with a wavelength of 940 to 950 nm. Two infrared light sources 112 are arranged at a position opposite to the dichroic mirror 28, and the near infrared light LA ​​is irradiated toward the dichroic mirror 28. Thus, the near infrared light LA ​​is irradiated toward the subject's eye E via the dichroic mirror 28 and one or more trial lenses 24b of the comprehensive ophthalmometer 14. Then, the return light of the near infrared light LA ​​from the subject's eye E travels in the opposite direction on the same path as the outgoing path and enters the objective lens 108.

[0137] The objective lens 108 emits the near infrared light LB with a wavelength of 840 nm incident from the light source system G2a described later toward the dichroic mirror 28. In addition, the near infrared light LA ​​and LB with two wavelengths reflected by the eye E enter the objective lens 108 via the first optical path LP1, the dichroic mirror 28, and the second optical path LP2. The near infrared light LA ​​and LB pass through the objective lens 108 and enter the dichroic mirror 107.

[0138] The dichroic mirror 107 transmits near infrared light LA ​​having a wavelength of 940 to 950 nm, and reflects near infrared light LB having a wavelength of 840 nm. Thus, the dichroic mirror 107 reflects near infrared light LB incident from the light source system G2a described later toward the objective lens 108. In addition, the dichroic mirror 107 allows the near infrared light LA ​​of the two wavelengths of near infrared light LA ​​and LB incident from the objective lens 108 to be incident on the anterior ocular segment observation system G1, and reflects the near infrared light LB toward the lens system 106. It should be noted that the reflected light of the visible band from the subject's eye E passes through the dichroic mirror 28 and is emitted to the outside of the wavefront sensor 100.

[0139] The anterior ocular segment observation system G1 includes a lens system 113 and an imaging element 114 .

[0140] The lens system 113 is simplified in the figure, but is an optical system composed of a plurality of lenses. This is also true for other lens systems described later. The lens system 113 forms an image on the light receiving surface of the imaging element 114 by causing the near infrared light LA ​​incident from the dichroic mirror 107 to be imaged.

[0141] The imaging element 114 is a well-known area sensor [e.g., a CCD (Charge Coupled Device) type image sensor], which receives (captures) the near-infrared light LA ​​formed by the lens system 113 and outputs a light reception signal representing an observed image of the anterior ocular portion of the subject's eye E to the image data output unit 115.

[0142] The light source system G2 a includes a light source 101 , a lens system 102 , a polarization beam splitter 104 , an aperture 105 , and a lens system 106 .

[0143] The light source 101 is a laser diode that emits near-infrared light LB having a wavelength of 830 to 840 nm. The lens system 102 converts the near-infrared light LB incident from the light source 101 into substantially parallel light and then emits the parallel light toward the polarization beam splitter 104 .

[0144] The polarization beam splitter 104 transmits, for example, S polarized light and reflects P polarized light. The polarization beam splitter 104 transmits the near infrared light LB incident from the lens system 102 toward the aperture 105. Thus, the near infrared light LB is irradiated toward the subject's eye E via the aperture 105, the lens system 106, the dichroic mirror 107, the objective lens 108, the dichroic mirror 28, and the phoropter 14. Then, the near infrared light LB (return light) reflected by the subject's eye E travels in the opposite direction on the same path as the outward path and enters the polarization beam splitter 104.

[0145] The polarization beam splitter 104 reflects the near-infrared light LB (P-polarized light) incident from the objective lens 108 toward the lens system 120 of the light receiving system G2 b .

[0146] The light receiving system G2 b shares the polarization beam splitter 104 with the light source system G2 a , and includes a lens system 120 , a Hartmann plate 121 , and an imaging element 122 .

[0147] The lens system 120 emits the near-infrared light LB incident from the polarization beam splitter 104 toward the Hartmann plate 121 .

[0148] A plurality of micro lenses having the same focal length are formed on the surface of the Hartmann plate 121 . The Hartmann plate 121 divides the near infrared light LB incident from the lens system 120 into a plurality of light beams corresponding to the respective micro lenses and forms an image of each light beam on the light receiving surface of the imaging element 122 .

[0149] The imaging element 122 is a well-known area sensor [for example, a CMOS (Complementary Metal Oxide Semiconductor) image sensor], which receives (images) a plurality of light beams formed on a light receiving surface by the Hartmann plate 121, and outputs light receiving signals representing a plurality of point images corresponding to each light beam to the image data output unit 115. Thus, the wavefront aberration of the subject's eye E representing the eye characteristics (eye refractive power, etc.) of the subject's eye E can be measured.

[0150] The image data output unit 115 outputs the image data of the observation image of the anterior ocular portion of the subject's eye E based on the light receiving signal input from the imaging element 114, and the image data of the Hartmann image based on the light receiving signal input from the imaging element 122 to the controller 11. It should be noted that the image data output unit 115 may also output to the controller 11 image data obtained by integrating the image data of the observation image of the anterior ocular portion and the image data of the Hartmann image. Thus, an anterior ocular image that allows visual grasp of the wavefront aberration can be obtained through the difference in local colors. Therefore, the pupil center in a strict sense can be used as the origin of the wavefront aberration display.

[0151] It should be noted that the corneal shape can be measured by attaching a keratoscope (not shown) as a member for measuring the corneal shape to the wavefront sensor 100. In this case, the image data output unit 115 has a function of outputting the measured corneal shape data in conjunction with the wavefront information.

[0152] The mirror control unit 116 drives an actuator (not shown) that rotates the dichroic mirror 28 left and right to control the rotation of the dichroic mirror 28. In addition, the mirror control unit 116 detects the rotation angle of the dichroic mirror 28 by a rotary encoder (not shown), and outputs the detection result to the image data output unit 115. Thus, data conversion can be performed by changing the coordinate axis (coordinate system) of the measurement result of the light receiving system G2b so that appropriate data can be obtained in the light receiving system G2b.

[0153] The tilt angle detection unit 117 includes a tilt angle sensor for detecting the tilt angle of the wavefront sensor 100, and outputs information on the tilt angle based on the detection result to the image data output unit 115. Thus, data conversion can be performed by changing the coordinate axis (coordinate system) of the measurement result of the light receiving system G2b so that appropriate data can be obtained in the light receiving system G2b.

[0154] [other]

[0155] In each of the above-described embodiments, the anterior ocular segment observation system 29A is provided in the wavefront sensor 20 , but the anterior ocular segment observation system 29A may be omitted. That is, the ophthalmologic apparatus of the present invention also includes an apparatus that does not include an observation system.

[0156] In the above-mentioned embodiments, the ophthalmic device of the present invention is composed of the controller 11 and each wavefront sensor 20, but the ophthalmic device of the present invention may also be composed of only each wavefront sensor 20. In this case, a wavefront sensor control unit 52 (which may also include a degree determination unit 50) is integrally provided with or built-in each wavefront sensor 20, and the wavefront sensor control unit 52 is connected to the controller 11 by wire or wirelessly.

[0157] In the above-described embodiments, the ophthalmologic system 9 for determining the prescription value of the eyeglass lenses or the like worn by the subject H1 is described as an example, but the present invention is also applicable to the ophthalmologic system 9 for other purposes.

[0158] In the above-mentioned embodiments, the connecting members 27 and 27A are detachably connected to the second inspection window 23 of each phoropter 14, but the hole, recess, convexity, protrusion, etc. provided on the rear side surface of the phoropter housing 25 opposite to the side facing the eye E to be inspected may be used as a connected member, and various connecting members may be detachably connected to the connected member. In this case, the connected member and the connecting member may be provided at positions different from those in the above-mentioned embodiments.

[0159] In the above-mentioned embodiments, the wavefront sensor 20 is cited as an example of the ophthalmic device (objective measurement system) of the present invention for explanation, but various well-known objective measurement systems including a refractometer for measuring the refractive power of the eye E to be examined, a keratometer for measuring the corneal shape of the eye E to be examined, an auto kerato-refractometer for measuring the refractive power and corneal shape, a fundus camera for taking a fundus photograph of the eye E to be examined, a three-dimensional fundus image capturing device for obtaining a tomographic image of the eye E to be examined, etc. may be connected to the comprehensive ophthalmometer 14.

[0160] Description of reference numerals:

[0161] 9...Ophthalmology System;

[0162] 11...Controller;

[0163] 14... Comprehensive optometry;

[0164] 20...Wavefront sensor;

[0165] 22...First inspection window;

[0166] 23...Second inspection window;

[0167] 23a... opening;

[0168] 24...Rotary disk mechanism;

[0169] 24a...Lens plate;

[0170] 24b...Trial lenses;

[0171] 25...Comprehensive ophthalmometer housing;

[0172] 26...sensor housing;

[0173] 27, 27A...Connecting components;

[0174] 28... dichroic mirror;

[0175] 29...wavefront sensor body;

[0176] 29A...Anterior ocular observation system;

[0177] 29B...Aberration measurement system;

[0178] 49...Comprehensive ophthalmometer control unit;

[0179] 50...Degree determination department;

[0180] 51...disk mechanism control unit;

[0181] 52...wavefront sensor control unit;

[0182] 54...Observation system control unit;

[0183] 56...Measurement system control unit;

[0184] 58...eye characteristic calculation unit;

[0185] 60...Re-measurement control unit;

[0186] 62 ... alignment detection unit;

[0187] 64... Alignment control unit;

[0188] 66...Relative movement mechanism;

[0189] 99...Infrared light source;

[0190] 130...Back cover.

Claims

1. An ophthalmic device connected to a corrective device for correcting the visual function of an eye to be inspected, the corrective device comprising two inspection windows arranged along an optical axis in pairs on the left and right, and a configuration mechanism for arranging one or more first optical elements between the two inspection windows, the two inspection windows comprising a first inspection window and a second inspection window in pairs on the left and right, the first inspection window being an inspection window for an eyepiece facing the eye to be inspected and arranged on a first side surface of the corrective device, the second inspection window being arranged on a second side surface of the corrective device on the opposite side of the first side surface of the corrective device, the corrective device further comprising openings surrounding corresponding second inspection windows on the second side surface of the corrective device in pairs on the left and right, wherein: The ophthalmic device comprises: a connecting member detachably connected to an opening portion surrounding the corresponding second inspection window on the second side surface of the correction device, the opening portion being provided on the second side surface of the correction device opposite to the first side surface of the correction device facing the eye to be examined; a second optical element, which is arranged at a position opposite to the second inspection window when the connecting member is connected to the opening on the second side surface of the correcting device, the second inspection window being an inspection window on the opposite side of the first inspection window for the eyepiece of the eye to be inspected, and which branches a second optical path from the first optical path along the optical axis; as well as The objective measurement system is arranged on the second optical path and acquires the eye characteristics of the eye to be inspected.

2. The ophthalmic device according to claim 1, wherein: The ophthalmic device includes a shell that accommodates the second optical element and the objective measurement system. When the back cover forming the side of the correction device on which the second inspection window is provided is removed from the correction device and the connecting member is connected to the second inspection window, the shell becomes a substitute for the back cover.

3. The ophthalmic device according to claim 1 or 2, wherein: The left and right second optical elements arranged on the optical axis for the left and right optical axes respectively branch the second optical path from the first optical path in directions parallel to both planes including the optical axes and away from each other.

4. The ophthalmic device according to claim 1 or 2, wherein: The ophthalmologic apparatus includes an output unit configured to output the eye characteristics acquired by the objective measurement system to a drive control unit that controls driving of the arrangement mechanism.

5. The ophthalmic device according to claim 1 or 2, wherein: The ophthalmologic apparatus includes an observation system for acquiring an observation image of the anterior ocular segment of the subject's eye. The ophthalmologic apparatus includes an alignment detection unit configured to detect a relative positional relationship between the eye to be inspected and the ophthalmologic apparatus based on the observation image acquired by the observation system.

6. The ophthalmic device according to claim 5, wherein: The ophthalmic device includes an alignment control unit, which is connected to a relative movement mechanism that causes one of the eye to be inspected and the corrective device to move relative to the other, and drives the relative movement mechanism based on the detection result of the alignment detection unit to align the ophthalmic device relative to the eye to be inspected.

7. The ophthalmic device according to claim 1, wherein: The center of the first inspection window and the center of the second inspection window are arranged along the same line.

8. The ophthalmic device according to claim 1, wherein: The connecting member is embedded in the corresponding opening on the second side surface of the correction device.

9. An ophthalmic system, wherein: The ophthalmic system comprises: A correction device that corrects the visual function of an eye to be inspected, and includes two inspection windows arranged along the optical axis in a left and right pair, and a configuration mechanism for arranging one or more first optical elements between the two inspection windows; as well as The ophthalmic device according to any one of claims 1 to 8.

Images