CN101569545A - Non-contact ultrasonic tonometer - Google Patents
Non-contact ultrasonic tonometer Download PDFInfo
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- CN101569545A CN101569545A CN 200910140516 CN200910140516A CN101569545A CN 101569545 A CN101569545 A CN 101569545A CN 200910140516 CN200910140516 CN 200910140516 CN 200910140516 A CN200910140516 A CN 200910140516A CN 101569545 A CN101569545 A CN 101569545A
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Abstract
A non-contact ultrasonic tonometer for measuring intraocular pressure of an examinee's eye in non-contact manner by use of an ultrasonic wave comprises: a probe including a vibrator for making the ultrasonic wave incident on the examinee's eye and a sensor for detecting the ultrasonic wave reflected from the examinee's eye; and an observation optical system for observing an anterior segment of the eye, wherein the probe is placed in an optical path of the observation optical system, and the observation optical system forms an image of the anterior segment through a surrounding region of the probe.
Description
Technical field
[0001] a kind of non-contact ultrasonic tonometer that is used for by the intraocular pressure of ultrasonic eyes with the non-contact mode measuring person of being looked into.
Background technology
[0002] a kind of being used for measures the contact intraocular pressure checkout facility of intraocular pressure and is suggested by push eyes with the end of probe pen, this probe pen keeps probe apparatus, and this probe apparatus comprises and is used for that vibration introduced the oscillator of eyes and is used to detect probe apparatus (checking patent documentation 1:JP2004-267299A) by the vibration detecting sensor of the vibration of eye reflections.
[0003] a kind of being used for by making ultrasound wave enter eyes (practically have also proposed, eyeball phantom) and by utilizing sensor (to check non-patent literature 1: " using the exploitation of the new contactless measure of intraocular pressure system of phase shift method " from the contactless measure of intraocular pressure system that the ultrasound wave of eye reflections is measured intraocular pressure, Masayuki JINDE and other three personnel, The Institution of Electrical Engineers's meeting, pick off and micro machine department, 93-96 page or leaf document, 2007).This system is configured to measurement along with the phase shift with respect to transmitted wave of the echo of frequency change, and the mutual relation between the hardness of the amount of definite frequency change and eye model.
[0004] yet, under the situation of the equipment of patent documentation 1 structure, make probe pen and eye contact with measurement intraocular pressure and thereby will be to the big load of eyes.The equipment structure of non-patent literature 1 is only to plan to measure eyeball phantom, and it is to be not enough to measure human eye.Reveal at meter under the situation of the human eye that involuntary eye movement and sight line move, may change owing to the misalignment of equipment and eyes, cause the variation of measurement result by the Ultrasonic characteristics (for example, frequency and phase place) of sensor.
Summary of the invention
Technical problem
[0005] the object of the invention is to provide and can easily makes the non-contact ultrasonic tonometer of tonometer with respect to the person's of being looked into eye alignment.
The solution of problem
[0006] for realizing above purpose, the invention provides a kind of being used for by utilizing the non-contact ultrasonic tonometer of ultrasound wave with the intraocular pressure of the non-contact mode measuring person's of being looked into eyes, this tonometer comprises: comprise that oscillator and being used on the eyes that are used to make this ultrasound wave be incident on this person of being looked into detects from the probe of hyperacoustic pick off of this person's of being looked into eye reflections; And the forward viewing optical system that is used to observe these eyes, wherein this probe is placed in the light path of this viewing optical system, and this viewing optical system is by the forward image of the regional formation of centering on of this probe.
Description of drawings
[0007] Fig. 1 is the three-dimensional external view of the non-contact ultrasonic tonometer of optimal case of the present invention;
Fig. 2 is the D structure figure of the measuring system and the optical system of tonometer;
Fig. 3 is the D structure figure (partly being block diagram) of the control system of tonometer;
Fig. 4 A and 4B are the figure that is presented at the example of the view screen that shows on the monitor;
Fig. 5 shows that object lens are placed on the figure of the situation behind the probe;
Fig. 6 is the figure that shows the variation of the fixed target projection optics system and the first alignment mark projection optics system;
Fig. 7 is the view of the situation that shows that probe is shifted with the direction perpendicular to the optical axis of viewing optical system;
Fig. 8 is the view that shows the situation outside the light path that is placed on viewing optical system of popping one's head in; And
Fig. 9 shows that tonometer is equipped with ophthalmic refractive power to measure the view of the situation of optical system.
The specific embodiment
[0008] preferred version of the present invention is described below with reference to the accompanying drawings.Fig. 1 is the spatial external view of the contactless ultrasonic tonometer 100 of this embodiment.
[0009] tonometer 100 is so-called fixed apparatuses, it comprises base 1, be attached to a support unit 2 of base 1, be provided in the removable unit 3 on the base 1 movably, and be provided in measurement component 4 on the removable unit 3 movably, and tonometer 100 optical system that comprises measuring system and mention subsequently.Measurement component 4 by be provided in the removable unit 3 moving-member 6 with respect to the right side of the person's of being looked into eye E and left to (directions X), upper and lower direction (Y direction), and back and the place ahead are to (operating distance direction; The Z direction) moves.Removable unit 3 is that the tilt operation by stick 5 moves with X and Z direction on base 1.Measurement component 4 is that the rotary manipulation by handle 5a is moved with the Y direction by moving-member 6.Stick 5 is equipped with on its top measures starting switch 5b.On pedestal 3 movably, be equipped with monitor 72.
[0010] Fig. 2 is the D structure view of the measuring system and the optical system of tonometer 100, shows the situation in the light path that is placed into viewing optical system of popping one's head in.Fig. 3 is the D structure view (part is a block diagram) of the control system of tonometer 100.
[0011] probe (pick off (transducer)) 10 that is placed on the person's of being looked into eye E front has and is used to make ultrasound wave (incidence wave, the transmission ripple) pick off (ultrasound wave acceptance division) 13 that is incident on the oscillator (ultrasound wave sending part) 11 on the eye E and is used to detect the ultrasound wave (echo receives ripple) that reflects by eye E.Probe 10 is to be that two piezoelectric elements on another constitute by for example arranging.One of them piezoelectric element is used as oscillator 11, and another is used as pick off 13.In this embodiment, impulse wave is used as the ultrasound wave that is incident on the eye E, but as an alternative, can use continuous wave.
[0012] more approaches on the side of eye E at probe 10, place acoustic lens (acoustic lens) 16 to assemble ultrasound wave from oscillator 11.When probe 10 and eye E were placed alignedly, these lens 16 became and focus on the eye E.
[0013] probe 10 is connected to amplifier 81, frequency content analysis portion 82, frequency plot difference specifying part 83, and computing and control part 70 in order.Amplifier 81 will be amplified to the appropriate signals level corresponding to the signal of telecommunication of incidence wave and echo and by analysis portion 82 it be carried out the frequency content analysis to obtain the spectrum distribution of phase contrast with respect to frequency.Specifying part 83 relatively the spectrum of incidence waves distribute and the spectrum distribution of echo with designated phase difference θ x, it is at the incidence wave of separately frequency f x and the phase contrast between the echo.To change (in fact strict, the variation of the hardness of the cornea of the person's of being looked into who produces by changing of intraocular pressure eye E) according to intraocular pressure at the phase contrast θ of frequency f x x.Correspondingly, computing and control part 70 are based on the output signal detected phase difference θ x of specifying part 83 and obtain the intraocular pressure of eye E based on this testing result.The method is with reference to US 6,854,331 (JP2002-272743A).
[0014] probe 10 and lens 16 (for example form porose 18 at center separately, round hole with diameter of about 1mm), it allows from the fixed target projection light of light source 32 (hereinafter, be called " fixed target light ") and pass through from the alignment mark projection light (being called hereinafter, " alignment mark light ") of light source 42.
[0015] oscillator 11 and pick off 13 usefulness distribution cables 95 be electrically connected to be arranged in viewing optical system 20 light path (hereinafter, be called " observation optical path ") outside Circuits System (amplifier 81, analysis portion 82, specifying part 83, computing and control part 70, and other).This cable 95 is covered by the covering 96 with the coating that is coated with the forward reflected light (for example, infrared light) that is used to absorb from eye E.This can prevent that spreading to be detected by the image pick-up device 26 of two dimension by the light that the front portion is reflected is noise light on the surface of cable 95.
[0016] being equipped with is the forward viewing optical systems 20 that are used to observe eye E as the optical system of tonometer 100, be used to the fixed target projection optics system 30 that makes eye E be maintained fixed, be used for to project the first alignment mark projection optics system 40 of eye E at the alignment mark of X and Y direction, be used for projecting the second alignment mark projection optics system 50 of eye E at the alignment mark of Z direction, and the alignment mark detection optical system 55 that is used to detect the Z direction alignment mark that projects on the eye E.
[0017] having wherein, the viewing optical system 20 of the light path of placement probe 10 forms forward image by the zone around probe 10.Specifically, viewing optical system 20 comprises, object lens 22, and imaging len 24, optical filter 25 and image pick-up device 26, and be equipped with the optical axis L 1 (being called hereinafter, " observation optical axis ") of wherein placing probe 10.So, when observation optical axis L1 and predetermined portions (for example, the CC of eye E or pupil center) on time, probe 10 is placed on the eye E front.In addition, in the structure of Fig. 2, probe 10 is configured to make the axis (extension of axis) of probe 10 and observation optical axis L1 coaxial.Thereby, when the predetermined portions of observation optical axis L1 and eye E on time, the axis of centres of probe 10 overlaps with the predetermined portions of eye E, so can detect the ultrasound wave that is reflected by eye E efficiently.
[0018] the emission infrared light is aligned to the front of eye E diagonally with the forward light source 38 of illumination eye E.Optical filter 25 has transmission from the light of each light source 38 with from the light of light source 42 and stop character from the light of light source 51.
[0019] is projected on the front portion of eye E from the light of each light source 38 and propagates towards lens 22 by the light of front portion reflection then.Arrive the light scioptics 22 in the zone on every side of probe 10, on image pick-up device 26, form image further by half-reflecting mirror 36 and dichroscope (dichroic mirror) 46, and by lens 24.Specifically, by the front image of light source 38 by pop one's head in 10 around the zone be formed on the image pick-up device 26.Dichroscope 46 has transmission from the light of each light source 38 with from the light of light source 42 and the reflection character from the light of light source 32.
[0020] the signal output from image pick-up device 26 is imported into computing and control part 70.The front image of picking up is displayed on the monitor 72.In the structure of Fig. 2, comprise that the imaging optical system (lens combination that is made of a plurality of lens) of lens 22 and 24 is used as the light transfer member that is used for front image is transported to image pick-up device 26.Alternatively, single lens can be used to front image is transported to image pick-up device 26.
[0021] for the relation of position on the direction (Z direction) of observation optical axis L1 between probe 10 and the lens 22, lens 22 be placed on probe 10 back (more near image pick-up device 26) or with probe 10 identical positions, can between the housing of eye E and equipment, be equipped with wideer space (checking Fig. 2 and 5) thus.In this case, can interrupt by probe 10 and lens 16 from forward reflected light.In order to allow clearly to observe front image, probe 10 and lens 22 preferably are to be placed in observation optical axis L1 to go up near each otherly, and are preferably and are placed on observation optical axis L1 and go up roughly the same position.
[0022] Fig. 2 shows wherein to pop one's head in and 10 is placed on an example of the structure of identical position with lens 22.That is to say that in its similar center, lens 22 are formed with the hole 22 of inserting probe 10 therein.In the 22a of this hole, be provided with probe 10 and lens 16.
[0023] Fig. 5 shows that lens 22 are placed on an example of the structure of probe 10 back.Specifically, in its similar center, lens 22 are formed with the hole 22 of inserting supporting member 19 therein.Probe 10 and lens 16 are set in the forward location in the supporting member 19 that is inserted among the 22a of hole.
[0024] alternatively, before lens 22 can be placed on probe 10.In this case, lens 22 preferably be in corresponding to the position of ultrasonic wave propagation path, form porose, to prevent lens 22 reflections and to weaken ultrasound wave from probe 10.So, be allowed to enter eye E and detect by the hole by pick off 13 from the incidence wave of oscillator 11 from the echo of eye E by the hole.
[0025] fixed target projection optics system 30 comprises at least fixed target is projected on the eye E so that eye E is observed the fixed target projection source of fixed target.Specifically, projection optics system 30 comprises light source 32, fixed target 33, and diaphragm 34, projection lens 35, and dichroscope 46 is to project fixed target on the eye E by hole 18.Make the optical axis L 2 of projection optics system 30 coaxial by the dichroscope 46 that is positioned at observation optical path with observation optical axis L1.
[0026] reduces by diaphragm 34 by light diameter, pass lens 35,, pass half-reflecting mirror 36, project on the bottom of eye E by hole 18 then by dichroscope 46 reflections from the light of the fixed target 33 of the visible illumination of light source 32.So, eye E is maintained fixed.
[0027] first alignment mark projection optics system 40 comprises that at least the alignment mark projection source is projecting on the eye E from the front at the alignment mark of X and Y direction.Specifically, projection optics system 40 comprises light source 42, and projection lens 44 and half-reflecting mirror 36 are to project alignment mark (alignment mark light) on the eye E by hole 18.Make the optical axis L 3 of projection optics system 40 coaxial by the half-reflecting mirror 36 that is positioned at observation optical path with observation optical axis L1.
[0028] infrared light from light source 42 passes lens 44, by half-reflecting mirror 36 reflections, is projected onto on the cornea of eye E by hole 18 then.Form image (alignment mark image) i1 of the virtual image (corneal reflex image) as light source 42 by the light of cornea direct reflection.
[0029] light of marking image i1 is propagated towards lens 22.Arrive probe 10 around the light in zone pass lens 22, half-reflecting mirror 36 and dichroscope 46, and on image pick-up device 26, form image by lens 24.In other words, by the marking image i1 of light source 42 by pop one's head in 10 around the zone be formed on the image pick-up device 26.When eye E when X and Y direction move, the image of marking image i1 forms the position and also moves on image pick-up device 26.Based on the detection signal of image pick-up device 26, computing and control part 70 can checkout equipments (probe 10) at X and the Y direction alignment with respect to eye E.
[0030] by being formed on the hole 18 projection alignment mark light in probe 10 and the lens 16 and receiving by the zone around the probe 10 under the catoptrical situation from eye E, a part of reflected light can be interrupted by lens 16.For avoiding such defective, as shown in Figure 2, projection optics system 40 preferably is configured to alignment mark light and can be got together then before arriving eye E and be projected onto optical system on the cornea as dispersed light.
[0031] second alignment mark projection optics system 50 comprises that at least the alignment mark projection source is projecting on the eye E from the direction that tilts at the alignment mark of Z direction.Specifically, projection optics system 50 comprises that light source 51 and projection lens 52 are to project alignment mark (alignment mark light) on the eye E.The optical axis L 4 of projection optics system 50 intersects with observation optical axis L1 at a predetermined angle.
[0032] from the infrared light scioptics 52 of light source 51, roughly collimated, be projected onto then on the cornea of eye E.Form image (alignment mark image) i2 of the virtual image (corneal reflex image) as light source 51 by the light of cornea direct reflection.
[0033] alignment mark detection optical system 55 comprises optical receiver lens 56, optical filter 57, and position sensitive device 58 (for example, circuit CCD) is to detect the alignment mark image that is formed by projection optics system 50.Optical filter 57 has transmission from the light of light source 51 and stop from the light of light source 38 with from the character of the light of light source 42.The optical axis L 5 of detection optical system 55 and the optical axis L 4 of projection optics system 50 are with respect to observation optical axis L1 symmetry.Optical axis L 5 intersects with the point of optical axis L 4 on optical axis L 1.
[0034] the marking image i2 of light source 51 is formed on the position sensitive device 58 by lens 56.When eye E when the Z direction moves, the image of marking image i2 forms the position and moves on position sensitive device 58.The detection signal of position-based sensitive device 58, computing and control part 70 can checkout equipments (probe 10) at the alignment of Z direction with respect to eyes.
[0035] computing and control part 70 are coupled to knob 5a, switch 5b, moving-member 6, monitor 72, specifying part 83, light source 32,38,42 and 51, image pick-up device 26, position sensitive device 58 is equipped with the operating portion (input part) 74 of various switches, as the memorizer 75 of storage part, and other.Computing and control part 70 carry out the control of entire equipment, the calculating of measured value, or the like.
[0036] memorizer 75 storages are presented at the phase contrast θ x of frequency f x and the form of the mutual relation between the intraocular pressure value.Computing and control part 70 are presented on the monitor 72 corresponding to the intraocular pressure value of detected phase contrast θ x and with the intraocular pressure value that retrieves from memorizer 75 retrievals based on the output signal of specifying part 83.
[0037] mutual relation between phase contrast θ x and the intraocular pressure value pre-determine the phase contrast θ x that obtains by this equipment on can be by experiment and the intraocular pressure value measured by the Goldmann tonometer between mutual relation be provided with.Memorizer 75 storages are used to use probe 10 to measure the program of intraocular pressure, are used to control the program of entire equipment, or the like.
[0038] on operation part 74, dispose and be used to select automatically aim at the automatic alignment pattern of measurement component 4 or manually aim at the selector switch 74a of the manual alignment pattern of measurement component 4 with respect to eye E with respect to eye E, be used to select and then aligned finishing just automatically to produce triggering signal with the automatic emission mode that begins to measure or based on the operating signal generating triggering signal of switch 5b selector switch 74b with the manual emission mode that begins to measure, and other.When having selected automatic emission mode, computing and control part 70 judge based on each detection signal of image pick-up device 26 and position sensitive device 58 whether alignment is suitable.Based on this result of determination, computing and control part 70 produces measures the beginning triggering signals, and based on the generation of this triggering signal, order probe 10 sends ultrasound wave to eye E.
[0039] the following operation of explaining equipment with above structure.At first, the person's of being looked into face (head) is fixed on the support unit 2.The scrutineer observes monitor 72 simultaneously by manipulation stick 5 makes equipment aim at the person's of being looked into eye E.At that time, computing and control part 70 show the front image of being picked up by image pick-up device 26 and are used for aligned graticule LT and designator G on monitor 72, shown in Fig. 4 A and 4B.
[0040] when marking image i1 begins to appear on the monitor 72 (when image pick-up device 26 beginning certification mark image i1) enable the automatic aligning in X and Y direction.In addition, when position sensitive device 58 beginning certification mark image i2, enable automatic aligning in the Z direction.Computing and control part 70 based on obtain from the detection signal of position sensitive device 58 about the information at the alignment of Z direction, the demonstration of control designator G.
[0041] the following situation of selecting automatic alignment pattern and automatic emission mode of explaining.Computing and control part 70 acquisition equipment are at X, and Y and Z direction are with respect to the amount of mis-alignment of the eye E that is positioned at suitable position, and the driving of control moving-member 6 is to introduce predetermined permissible range with each amount of mis-alignment.In the time of within each amount of mis-alignment drops on this permissible range, computing and control part 70 stop the driving of moving-member 6 and automatically produce measuring the beginning triggering signal with the beginning measure of intraocular pressure.
[0042] the following situation of selecting manual alignment pattern and manual emission mode of explaining.In this case, scrutineer's manipulation bar 5 (knob 5a) is so that (referring to Fig. 4 B) appears in the form that marking image i1 enters among the graticule LT and designator G finishes with the representative aligning that is presented on the monitor 72.Aim at and during by scrutineer's push switch 5b, computing and control part 70 produce measures the beginning triggering signals with the beginning measure of intraocular pressure when all having finished in each direction.
[0043] and then measure the generation that begins triggering signal, computing and control part 70 make oscillator 11 emission ultrasound wave detect the ultrasound wave that reflects from eye E to eye E and by pick off 13.Computing and control part 70 calculate the intraocular pressure value of eye E based on the output signal of specifying part 83 and its result are presented on the monitor 82.
[0044] uses above structure, can easily carry out eye E and the aligning between 10 of popping one's head in.
[0045] in above explanation, fixed target light is projected onto on the eye E by the hole 18 that is formed on probe 10 center.Needn't be limited to this, also can be configured to the zone projection fixed target light on every side of the probe 10 in the scioptics 22.The structure of expecting in this case is, for example, uses the diaphragm with center annular aperture on optical axis L 2, replaces having the diaphragm 34 in the point-like hole on optical axis L 2.
[0046] in above embodiment, alignment mark light is projected onto on the eye E by the hole 18 that is formed on probe 10 center.Be not necessarily limited to this, also can be configured to the zone projection alignment mark light on every side of the probe 10 in the scioptics 22, and allow image pick-up device 26 to detect the reflected light in the zone on every side of the probe 10 in the scioptics 22.The structure that can expect is in this case, for example, uses annular light source to replace point source 42.
[0047] Fig. 6 is the view that shows the variation of the fixed target projection optics system and the first alignment mark projection optics system.In this case, light source 32 (for example, LED) is placed on the center of probe 10.
[0048] the first alignment mark projection optics system 140 that is used for alignment mark light is projected at a predetermined angle observation optical axis L1 is placed on lens 22 outsides.Its reflected light is allowed to pass through the zone on every side of the probe 10 in the lens 22.In this case, the angle of the optical axis of projection optics system 140 and observation optical axis L1 is determined to prevent that partial reflection light from becoming by lens 16 and interrupts.
[0049] be placed in the situation at center of probe 10 at as shown in Figure 6 light source 32, the light source that sends visible light and infrared light can be as light source 32 with as fixed target projection source and alignment mark projection source.
[0050] in above explanation, probe 10 is placed on the observation optical axis L1, yet is not limited to this.Probe 10 can be shifted from observation optical axis L1 with the direction (X and Y direction) perpendicular to optical axis L 1, as shown in Figure 7.In this case, when probe 10 the axis of centres (extension of the axis of centres) become with the predetermined portions of eye E (for example, CC or pupil center) punctual marking image i1 detection position on image pick-up device 26 is set up as aiming at the reference position, and the display position of graticule LT is set, aim at the completing place, and other.
[0051] Fig. 8 is the structural map of the signal of the measuring system of tonometer 100 and optical system, shows that probe is placed on the outer situation of light path of viewing optical system.
[0052] ultrasonic reflections member (acoustic mirror) 90 reflects the echo that reflects from eye E towards pick off 13 from the incidence wave while of oscillator 11 towards eye E.Viewing optical system 20 is configured to so that pop one's head in and 10 be placed on the outer and observation optical axis L1 of its light path and be positioned on the ultrasonic wave propagation path between reflecting member 90 and the eye E.Lens 22 are formed with the hole 22b that permission is passed from probe 10 ultrasound wave.Incidence wave from oscillator 11 is reflected member 90 reflections to enter eye E after passing hole 22b.Echo from eye E passes hole 22b, and member 90 reflections that are reflected are detected by pick off 13 then.
[0053] in lens 22 are placed on situation between reflecting member 90 and the eye E, in corresponding to the part of ultrasonic wave propagation path, form the ultrasound wave that the lens 22 of porose 22b can avoid may causing and weaken in the process of scioptics 22.In this case, be coated with and have the reflecting member 90 that stops from the coating of the catoptrical character of forward light source 38 and can be used to prevent that anterior reflected light from entering image pick-up device 26 by hole 22b, prevent the noise light that produces thus.
[0054], can use the member (for example, transparent, hard plastic plate) of character with reflection supersonic wave and transillumination with colourless about reflecting member 90.Even when reflecting member 90 is placed in each light path of projection optics system 30 and projection optics system 40, this can prevent also that fixed target light and alignment mark light from becoming and be interrupted.Have in use under the situation of reflecting member 90 of transmitance matter, consider that light path is changed by the transmission of the light by reflecting member 90, can use to have almost to equal for example member of the optical path split area of members of half-reflecting mirror 36 and dichroscope 46.
[0055] the invention is not restricted to above structure and can be configured to allow fixed target light and alignment mark light to pass to be projected onto the hole on the eye E so that reflecting member 90 partly is equipped with.More than structure shows that reflecting member 90 is placed into the situation in the shared light path of projection optics system 30 and 40.More than structure can be applied to the situation at least one the light path that reflecting member 90 is placed in projection optics system 30 and 40.
[0056] probe 10 is placed on the structure that the outer structure of observation optical path is not limited to show among Fig. 8 and can be configured to so that reflecting member 90 is placed between lens 22 and the eye E.In this case, be reflected member 90 reflections to enter eye E, simultaneously from be reflected member 90 reflections and detect of the echo of eye E by pick off 13 from the incidence wave of oscillator 11.
[0057] tonometer can be equipped with the measurement optical system that is used to measure the eyes characteristic that is different from intraocular pressure in addition.Fig. 9 shows that ophthalmic refractive power measurement optical system is added to the view of the situation of tonometer.
[0058] ophthalmic refractive power is measured optical system 310 and is configured to so that pop one's head in and 10 be placed on outside the light path (measurement light path) of measuring optical system 310, and the optical axis L 6 (being called hereinafter, " measurement optical axis ") of measuring optical system 310 is on the ultrasonic wave propagation path between reflecting member 90 and the eye E.Reflecting member 90 is placed on the eye E front.Be reflected member 90 reflections to enter eye E and from be reflected member 90 reflections and detect by pick off 13 of the echo of eye E from the incidence wave of oscillator 11.So, the intraocular pressure of eye E is measured.
[0059] measures on the transmissive side of dichroscope 301 at rear that optical system 310 is held in place reflecting member 90.Measure optical system 310 and be and be used for measuring light is projected the bottom of eye E and receives catoptrical optical system from the bottom by optical pickup apparatus.Based on the output signal of optical pickup apparatus, ophthalmic refractive power is measured.Measure optical system 310 and ophthalmic refractive force measurement principle and be well-known and thereby their details here omit.
[0060] on the reflection side of dichroscope 301, object lens 311 have been placed, dichroscope 312, and completely reflecting mirror 313.On the reflection side of mirror 313, disposed the fixed target projection optics system that does not show and observed fixed target to make eye E.
[0061] on the reflection side of dichroscope 312, configuration be viewing optical system 322, it comprise with eye E forward near the imaging len 320 placed of roughly conjugated relation and the image pick-up device 321 of two dimension.Image pick-up device 321 picks up front image that is formed by light source 325 and the marking image that is formed by the alignment mark projection optics system that does not show.
[0062] make the measurement optical axis L6 of viewing optical system 322 and optical axis L 7 coaxial by dichroscope 301.Dichroscope 301 has the light of transmission from the light source of measuring optical system 310, and reflection is from the light of light source 325, from the light of the light source of alignment mark projection optics system and from the character of the light of the light source of fixed target projection optics system.Dichroscope 312 also have transmission from the light of the light source of fixed target projection optics system and reflection from the light of light source 325 with from the character of the light of the light source of alignment mark projection optics system.As reflecting member 90 are member with character of reflection supersonic wave and transillumination (for example, transparent in colourless, hard plastic plate).The measuring light of this member transmission measurement optical system 310, the anterior reflected light of light source 325, the fixed target light of fixed target projection optics system, the alignment mark light of alignment mark projection optics system, and other.
[0063] in the structure of Fig. 9, reflecting member 90 is placed on measures optical system 310, in the shared light path of viewing optical system 322 and fixed target projection optics system, but whether is limited to this.This structure only must be by reflecting member 90 reflection from the ultrasound wave of probe 10 to enter eye E from the front.For example, reflecting member 90 can be placed between dichroscope 301 and the lens 311.
[0064] measures optical system though ophthalmic refractive power is for example understood in above explanation, the invention is not restricted to this and can be applied to being used for by receiving the measurement optical system that the reflected light measurement that is produced by the measuring light that projects on the eye E is different from the eyes characteristic of intraocular pressure.For example, and non-contact type eyes axial length measurement optical system (for example, referring to US 7,434,932 (JP2007-37984A), corneal thickness is measured optical system (for example, referring to JP63-197433 (1988) A), reaches can being used of other.
[0065] in addition, can be as required carrying out carrying out the normal measurement pattern of a measure of intraocular pressure in response to a triggering signal and selecting the pattern of carrying out measure of intraocular pressure that starts triggering signal based on measuring in response to a triggering signal between with the continuous measurement pattern of measure of intraocular pressure repeated several times with switch etc.
[0066] the following situation of selecting the continuous measurement pattern of explaining.And then measure the generation that starts triggering signal, computing and control part 70 order probes 10 continuously send ultrasonic pulse obtaining the information of the relevant changing of intraocular pressure that is caused by the pulsation of eye E to eye E, and carry out the calculation process corresponding to each ultrasonic pulse that continuously sends.
[0067] specifically, with within the scope of pulsation period of eye E (for example, 1.5 within second) predetermined time interval (for example, 0.1 second at interval) make ultrasonic pulse continuously be incident on the eye E, and calculate intraocular pressure value corresponding to each ultrasonic pulse.In this way, can in the pulsation period scope, obtain a lot of intraocular pressure value and thereby can catch the variation of the intraocular pressure value in the pulsation period.In this case, based on each measured value that in the pulsation period scope, obtains, can calculate representative value (for example, the meansigma methods of measured value, the central value of measured value) and calculate peak, the end and the intermediary measured value of pulsing.
[0068] in above explanation, ultrasonic pulse is to send with predetermined time interval (for example, 0.1 second at interval), yet is not limited to this.Ultrasonic pulse can send with the pre-determined number that sets in advance in the pulsation period scope.Can make the interval about continuously launching ultrasonic pulse is the permutator that at random can be provided with and can be equipped with it in operation part 74 with sending number.
[0069] in above explanation, on the Z direction equipment with respect to the alignment of eye E detected optically (operating distance is detected) but it can detect by the probe 10 that is used for measure of intraocular pressure.In this case, probe 10 control must be used to measure control of intraocular pressure and be used for being converted between the control of testing distance.By utilizing probe 10 to detect under the situation with respect to the operating distance of eye E, computing and control part 70 measure since the incidence wave of oscillator 11 towards eye E sent until from the echo of eye E by the Measuring Time T of pick off 13 detections and thus detection probe 10 leave the operating distance of eye E.In other words, since oscillator 11 hyperacoustic sent until ultrasound wave longlyer by the Measuring Time T that pick off 13 detects, operating distance is bigger.Measuring Time T is shorter, and operating distance is littler.Computing and control part 70 pre-determine reference measurement time T k, and for it, operating distance is suitable with respect to eye E, and when Measuring Time T reaches reference measurement time T k, and computing and control part 70 think that the aligning in the Z direction is done.
[0070] under the situation of above structure, for example, computing and control part 70 are controlled probe 10 as controlling probe 10 as the measure of intraocular pressure pick off with respect to eye E with respect to the operating distance pick off of eye E and after aligning is finished before aligning is finished.This can simplify and is used for the structure of checkout equipment about the alignment on the Z direction of eye E.
[0071] does above explanation to determine intraocular pressure based on the difference of the acoustic impedance that produces from the phase contrast between input phase and the output phase.The invention is not restricted to this and can be applied to can be by the comparison of the echo that carries out detecting from the incidence wave of oscillator 11 with by pick off 13 and the structure that calculation process is determined intraocular pressure.For example, it can be configured to determine intraocular pressure by the comparison and the calculation process of the reflection wave frequency of carrying out detecting from the incident wave frequency of oscillator 11 with by pick off 13.Specifically, can be equipped with phase-shift circuit phase contrast is moved to zero by when between to the input oscillogram of oscillator 11 and output waveform, phase contrast occurring, changing the frequency of ultrasonic that produces by oscillator 11 from pick off 13.Intraocular pressure is to determine by the frequency variation that detects when phase contrast is moved to zero.
Claims (8)
1. non-contact ultrasonic tonometer is used for it is characterized in that by utilizing the intraocular pressure of ultrasound wave with the non-contact mode measuring person's of being looked into eyes described tonometer comprises:
Comprise that oscillator and being used on the eyes that are used to make described ultrasound wave be incident on the described person of being looked into detects from the probe of described hyperacoustic pick off of the described person's of being looked into eye reflections; And
Be used to observe the forward viewing optical system of described eyes,
Wherein said probe is placed in the light path of described viewing optical system, and
Described viewing optical system forms described forward image by the peripheral region of described probe.
2. tonometer as claimed in claim 1 is characterized in that,
Described probe is placed on the optical axis of described viewing optical system.
3. tonometer as claimed in claim 2 is characterized in that,
Described probe is placed as and makes its axis and the described optical axis of described viewing optical system coaxial.
4. tonometer as claimed in claim 1 is characterized in that,
The object lens that described viewing optical system comprises image pick-up device and be used for forming described front image on described image pick-up device, and
Described object lens have the hole, insert described probe in described hole.
5. tonometer as claimed in claim 1 is characterized in that,
The object lens that described viewing optical system comprises image pick-up device and be used for forming described front image on described image pick-up device, and
Described object lens are placed on before the described probe and have the hole that allows described ultrasound wave to pass through.
6. tonometer as claimed in claim 1 is characterized in that, further comprises being equipped with being used for fixed target projected on the described eyes so that described eyes are observed the fixed target projection optics system of light source of the fixed target projection of described fixed target,
Wherein said probe has the hole that permission is passed through from the fixed target light of described light source.
7. tonometer as claimed in claim 1 is characterized in that, comprises further being equipped with the alignment mark projection optics system that is used for alignment mark is projected the light source of the alignment mark projection on the described eyes, and
The alignment mark detection optical system of the image pick-up device of the corneal reflex image that detection forms by described light source is equipped with,
Wherein said viewing optical system forms described corneal reflex image by the described peripheral region of described probe on described image pick-up device.
8. tonometer as claimed in claim 7 is characterized in that,
Described probe has the hole that permission is passed through from the alignment mark light of described light source.
Applications Claiming Priority (6)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2008-120794 | 2008-05-03 | ||
| JP2008-120793 | 2008-05-03 | ||
| JP2008120794 | 2008-05-03 | ||
| JP2008120793A JP5410692B2 (en) | 2008-05-03 | 2008-05-03 | Non-contact ultrasonic tonometer |
| JP2008120794A JP5117275B2 (en) | 2008-05-03 | 2008-05-03 | Non-contact ultrasonic tonometer |
| JP2008120793 | 2008-05-03 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN101569545A true CN101569545A (en) | 2009-11-04 |
| CN101569545B CN101569545B (en) | 2014-03-19 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN200910140516.5A Expired - Fee Related CN101569545B (en) | 2008-05-03 | 2009-04-30 | Non-contact ultrasonic tonometer |
Country Status (2)
| Country | Link |
|---|---|
| JP (1) | JP5410692B2 (en) |
| CN (1) | CN101569545B (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN104027067A (en) * | 2014-05-29 | 2014-09-10 | 温州眼视光发展有限公司 | Human eye front tissue coaxial imaging, fixation and lighting system |
| CN104367347A (en) * | 2014-05-16 | 2015-02-25 | 深圳大学 | System and method for measuring intra-ocular pressure and cornea viscoelasticity |
| CN106061399A (en) * | 2014-01-22 | 2016-10-26 | 模拟技术公司 | Imaging apparatus and interventional instrument event mapper |
| CN110996761A (en) * | 2017-06-13 | 2020-04-10 | 伊利诺伊大学董事会 | Non-mydriatic, non-contact system and method for performing wide-field fundus photographic imaging of an eye |
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| JP5562703B2 (en) * | 2010-03-31 | 2014-07-30 | 株式会社ニデック | Non-contact ultrasonic tonometer |
| AU2016233280B2 (en) * | 2015-03-16 | 2021-03-25 | Magic Leap, Inc. | Augmented reality pulse oximetry |
| KR102379691B1 (en) | 2016-04-08 | 2022-03-25 | 매직 립, 인코포레이티드 | Augmented reality systems and methods with variable focus lens elements |
| JP6723843B2 (en) * | 2016-06-22 | 2020-07-15 | 株式会社トプコン | Ophthalmic equipment |
| CN110537122B (en) | 2017-02-23 | 2022-04-29 | 奇跃公司 | Variable-focus virtual image device based on polarization conversion |
| EP3856040B1 (en) | 2018-09-28 | 2024-01-03 | Nidek Co., Ltd. | Ultrasonic tonometer and ultrasonic actuator |
| JP7334777B2 (en) | 2018-09-28 | 2023-08-29 | 株式会社ニデック | Ultrasonic tonometer and ultrasonic actuator |
| JP7375321B2 (en) * | 2019-03-28 | 2023-11-08 | 株式会社ニデック | intraocular pressure measuring device |
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| JPS6264332A (en) * | 1985-09-13 | 1987-03-23 | キヤノン株式会社 | Ophthalmic measuring apparatus |
| US4928697A (en) * | 1988-09-28 | 1990-05-29 | The Ohio State University | Non-contact high frequency tonometer |
| JPH04114625A (en) * | 1990-09-04 | 1992-04-15 | Canon Inc | Ophthalmological apparatus |
| JPH04114626A (en) * | 1990-09-04 | 1992-04-15 | Canon Inc | Ophthalmologic apparatus |
| JPH05253190A (en) * | 1991-10-10 | 1993-10-05 | Massie Res Lab Inc | Non-contact type tonometer |
| JPH11113846A (en) * | 1997-10-09 | 1999-04-27 | Topcon Corp | Ophthalmologic device |
| EP1327412B1 (en) * | 2002-01-10 | 2007-08-15 | Carl Zeiss Meditec AG | Apparatus for illuminating the lens of a human eye |
| JP4126249B2 (en) * | 2003-05-30 | 2008-07-30 | 株式会社ニデック | Ophthalmic equipment |
| US20050020896A1 (en) * | 2003-07-24 | 2005-01-27 | Fuller Terry A. | Apparatus and method of intraocular pressure determination |
| JP5505684B2 (en) * | 2006-12-08 | 2014-05-28 | 学校法人日本大学 | Tonometry device |
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Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106061399A (en) * | 2014-01-22 | 2016-10-26 | 模拟技术公司 | Imaging apparatus and interventional instrument event mapper |
| US10470824B2 (en) | 2014-01-22 | 2019-11-12 | BK Medical Holding Company | Imaging apparatus and interventional instrument event mapper |
| CN104367347A (en) * | 2014-05-16 | 2015-02-25 | 深圳大学 | System and method for measuring intra-ocular pressure and cornea viscoelasticity |
| CN104367347B (en) * | 2014-05-16 | 2016-12-07 | 深圳大学 | A kind of measurement intraocular pressure and the viscoelastic system and method for cornea |
| CN104027067A (en) * | 2014-05-29 | 2014-09-10 | 温州眼视光发展有限公司 | Human eye front tissue coaxial imaging, fixation and lighting system |
| CN110996761A (en) * | 2017-06-13 | 2020-04-10 | 伊利诺伊大学董事会 | Non-mydriatic, non-contact system and method for performing wide-field fundus photographic imaging of an eye |
| CN110996761B (en) * | 2017-06-13 | 2022-05-13 | 伊利诺伊大学董事会 | Non-mydriatic, non-contact system and method for performing wide-field fundus photographic imaging of an eye |
| US11974809B2 (en) | 2017-06-13 | 2024-05-07 | The Board Of Trustees Of The University Of Illinois | Non-mydriatic, non-contact system and method for performing widefield fundus photographic imaging of the eye |
Also Published As
| Publication number | Publication date |
|---|---|
| CN101569545B (en) | 2014-03-19 |
| JP2009268651A (en) | 2009-11-19 |
| JP5410692B2 (en) | 2014-02-05 |
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