CN101569545B - Non-contact ultrasonic tonometer - Google Patents
Non-contact ultrasonic tonometer Download PDFInfo
- Publication number
- CN101569545B CN101569545B CN200910140516.5A CN200910140516A CN101569545B CN 101569545 B CN101569545 B CN 101569545B CN 200910140516 A CN200910140516 A CN 200910140516A CN 101569545 B CN101569545 B CN 101569545B
- Authority
- CN
- China
- Prior art keywords
- probe
- eye
- optical system
- light
- tonometer
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Images
Landscapes
- Eye Examination Apparatus (AREA)
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 theeye, 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 pr obe.
Description
Technical field
A kind of non-contact ultrasonic tonometer for the intraocular pressure by the ultrasonic eyes with the non-contact mode measuring person of being looked into.
Background technology
A kind ofly for measure the contact intraocular pressure checkout facility of intraocular pressure by press eyes with the end of probe pen, be suggested, this probe pen keeps probe apparatus, and this probe apparatus comprises for vibration being introduced to the oscillator of eyes and for detection of the probe apparatus (checking patent documentation 1:JP2004-267299A) of the vibration detecting sensor of the vibration by eye reflections.
What also propose to have is a kind of for by making ultrasound wave enter eyes (practically, eyeball phantom) and by utilizing sensor to detect the contactless measure of intraocular pressure system of measuring intraocular pressure from the ultrasound wave of eye reflections (check non-patent literature 1: " using the exploitation of the new contactless measure of intraocular pressure system of phase shift method ", Masayuki JINDE and other three personnel, the Institution of Electrical Engineers's meeting, sensor and micro machine department, 93-96 page document, 2007).This system is configured to measure along with the phase shift with respect to transmitted wave of the echo of frequency change, and the mutual relation between the amount of definite frequency change and the hardness of eye model.
Yet, in the situation that the equipment of patent documentation 1 structure, make probe pen and eye contact to measure intraocular pressure and thereby by the large load of eyes.The equipment structure of non-patent literature 1 is only to intend to measure eyeball phantom, and it is to be not enough to measure human eye.In the situation that meter reveals the human eye that involuntary eye movement and sight line move, the Ultrasonic characteristics being detected by sensor (for example, frequency and phase place) may change due to the misalignment of equipment and eyes, causes the variation of measurement result.
Summary of the invention
Technical problem
The object of the invention is to provide and can easily makes tonometer with respect to the non-contact ultrasonic tonometer of the person's of being looked into eye alignment.
The solution of problem
For realizing above object, the invention provides a kind ofly for by utilizing ultrasound wave with the non-contact ultrasonic tonometer of the intraocular pressure of the non-contact mode measuring person's of being looked into eyes, this tonometer comprises: comprise for making this ultrasound wave be incident on oscillator on this person's of being looked into eyes and for detection of the probe of hyperacoustic sensor of the eye reflections from this person of being looked into; And for observing the anterior viewing optical system of these eyes, wherein this probe is placed in the light path of this viewing optical system, and this viewing optical system forms anterior image by this probe around region.
Accompanying drawing explanation
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 measuring system and the optical system of tonometer; Fig. 3 is the D structure figure (being partly 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 showing on monitor; Fig. 5 shows that object lens are placed on the figure of the situation after probe; Fig. 6 is the figure that shows the variation of 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 of the optical axis perpendicular to viewing optical system; Fig. 8 shows that probe is placed on the view of the situation outside the light path of viewing optical system; 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
Preferred version of the present invention is described below with reference to the accompanying drawings.Fig. 1 is the three-dimensional external view of the contactless ultrasonic tonometer 100 of this embodiment.
Fig. 2 is the D structure view of measuring system and the optical system of tonometer 100, shows that probe is placed into the situation in the light path of viewing optical system.Fig. 3 is the D structure view (part is block diagram) of the control system of tonometer 100.
The probe (sensor (transducer)) 10 being placed on before the person's of being looked into eye E has for making ultrasound wave (incidence wave, send ripple) be incident on oscillator (ultrasound wave sending part) 11 in eye E and for detection of the sensor (ultrasound wave acceptance division) 13 of the ultrasound wave being reflected by eye E (echo receives ripple).Probe 10 is by for example arranging, to be that two piezoelectric elements on another form.One of them piezoelectric element is used as oscillator 11, and another is used as sensor 13.In this embodiment, impulse wave is used as being incident on the ultrasound wave in eye E, but as an alternative, can use continuous wave.
In side at probe 10 closer to eye E, place acoustic lens (acoustic lens) 16 to assemble the ultrasound wave from oscillator 11.When probe 10 and eye E are placed alignedly, these lens 16 become and focus in eye E.
Be equipped with is for observing the anterior viewing optical system 20 of eye E as the optical system of tonometer 100, for making eye E keep fixing fixed target projection optics system 30, for the alignment mark in X and Y-direction being projected to the first alignment mark projection optics system 40 of eye E, for the alignment mark in Z direction being projected to the second alignment mark projection optics system 50 of eye E, and for detection of the alignment mark detection optical system 55 that projects the Z direction alignment mark in eye E.
The viewing optical system 20 with the light path of wherein placing probe 10 forms anterior image by the region 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 (below, being called " observation optical axis ") of wherein placing probe 10.So, for example, when observation optical axis L1 and predetermined portions (, the CC of eye E or pupil center) are on time, probe 10 is placed on before eye E.In addition,, in the structure of Fig. 2, probe 10 be configured to make to pop one's head in 10 axis (extension of axis) is coaxial with observation optical axis L1.Thereby when the predetermined portions of observation optical axis L1 and eye E is on time, the axis of centres of probe 10 overlaps with the predetermined portions of eye E, so can detect efficiently the ultrasound wave being reflected by eye E.
Transmitting infrared light with illumination eye E anterior light source 38 be aligned to diagonally eye E before.Optical filter 25 has transmission from the light of each light source 38 with from the light of light source 42 and stop the character from the light of light source 51.
From the light of each light source 38, being projected to the light then being reflected by front portion on the front portion of eye E propagates towards lens 22.The light scioptics 22 in the region of the surrounding of arrival probe 10 further by half-reflecting mirror 36 and dichroscope (dichroic mirror) 46, and form image by lens 24 on image pick-up device 26.Specifically, by the front image of light source 38, the region by 10 the surrounding of popping one's head in is formed on image pick-up device 26.Dichroscope 46 have transmission from the light of each light source 38 and from the light of light source 42 and reflection the character from the light of light source 32.
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 monitor 72.In the structure of Fig. 2, comprise that the imaging optical system (lens combination consisting of a plurality of lens) of lens 22 and 24 is used as for front image being transported to the light transfer member of image pick-up device 26.Alternatively, single lens can be used to front image to be transported to image pick-up device 26.
Relation for the position in the direction (Z direction) of observation optical axis L1 between probe 10 and lens 22, lens 22 be placed on after probe 10 (more approaching image pick-up device 26) or with probe 10 identical positions, can between eye E and the housing of equipment, be equipped with wider space (checking Fig. 2 and 5) thus.In this case, from anterior reflected light, can be interrupted by probe 10 and lens 16.In order to allow clearly to observe front image, it is upper near each other that probe 10 and lens 22 are more preferably placed in observation optical axis L1, and be preferably and be placed on the upper roughly the same position of observation optical axis L1.
Fig. 2 show wherein pop one's head in 10 and lens 22 be placed on an example of the structure of identical position.That is to say, in its similar center, lens 22 are formed with the hole 22 of inserting therein probe 10.In the 22a of this hole, be provided with probe 10 and lens 16.
Fig. 5 shows that lens 22 are placed on an example of probe 10 structure below.Specifically, in its similar center, lens 22 are formed with the hole 22 of inserting therein supporting member 19.Probe 10 and lens 16 are arranged in the forward location in the supporting member 19 being inserted in the 22a of hole.
Alternatively, lens 22 can be placed on before probe 10.In this case, lens 22 more preferably form porose in the position corresponding to ultrasonic wave propagation path, to prevent that lens 22 from reflecting and weakening from probe 10 ultrasound wave.So, from the incidence wave of oscillator 11, being allowed through hole enters eye E and by hole, is detected by sensor 13 from the echo of eye E.
Fixed target projection optics system 30 at least comprises and fixed target being projected in 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 in eye E by hole 18.By being positioned at the dichroscope 46 of observation optical path, make the optical axis L 2 of projection optics system 30 coaxial with observation optical axis L1.
Light diameter by the light of the fixed target 33 of the visible illumination from light source 32 is reduced by diaphragm 34, through lens 35, by dichroscope 46, is reflected, and through half-reflecting mirror 36, then by hole 18, projects on the bottom of eye E.So, eye E keeps fixing.
The first alignment mark projection optics system 40 at least comprise alignment mark projection source with by the alignment mark in X and Y-direction from projecting eye E above.Specifically, projection optics system 40 comprises light source 42, projection lens 44, and half-reflecting mirror 36 is to project alignment mark (alignment mark light) in eye E by hole 18.By being positioned at the half-reflecting mirror 36 of observation optical path, make the optical axis L 3 of projection optics system 40 coaxial with observation optical axis L1.
Infrared light from light source 42 passes lens 44, by half-reflecting mirror 36, is reflected, and then by hole 18, is projected onto on the cornea of eye E.By the light of cornea direct reflection, formed image (alignment mark image) i1 of the virtual image (corneal reflex image) as light source 42.
The light of marking image i1 is propagated towards lens 22.The light in the region of the surrounding of arrival probe 10 passes 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 the region of 10 the surrounding of popping one's head in, be formed on image pick-up device 26.When eye E is when X and Y-direction move, the image of marking image i1 forms position and also on image pick-up device 26, moves.Detection signal based on image pick-up device 26, computing and control part 70 can checkout equipments (probe 10) in X and the Y-direction alignment with respect to eye E.
By being formed on the region of hole 18 projection alignment mark light in probe 10 and lens 16 and the surrounding by probe 10, receiving in the catoptrical situation from eye E, a part of reflected light can be interrupted by lens 16.For avoiding such defect, as shown in Figure 2, projection optics system 40 is preferably configured to alignment mark light and is converged once and then as dispersed light, is projected onto the optical system on cornea before arriving eye E.
The second alignment mark projection optics system 50 at least comprises that alignment mark projection source is to project the alignment mark in Z direction eye E from the direction tilting.Specifically, projection optics system 50 comprises that light source 51 and projection lens 52 are to project alignment mark (alignment mark light) in eye E.The optical axis L 4 of projection optics system 50 intersects with observation optical axis L1 at a predetermined angle.
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 being formed by projection optics system 50.Optical filter 57 has transmission from the light of light source 51 and stops 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 is symmetrical with respect to observation optical axis L1 with the optical axis L 4 of projection optics system 50.Optical axis L 5 intersects with the point of optical axis L 4 in optical axis L 1.
The marking image i2 of light source 51 is formed on position sensitive device 58 by lens 56.When eye E is when Z direction moves, the image of marking image i2 forms position and moves in position sensitive device 58.The detection signal of position-based sensitive device 58, computing and control part 70 can the alignment of checkout equipment (probe 10) in Z direction with respect to eyes.
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 whole equipment, the calculating of measured value, etc.
Memorizer 75 storages are presented at the phase contrast θ x of frequency f x and the form of the mutual relation between intraocular pressure value.Computing and the output signal of control part 70 based on specifying part 83 are retrieved corresponding to the intraocular pressure value of the phase contrast θ x detecting and the intraocular pressure value retrieving are presented at monitor 72 from memorizer 75.
The mutual relation that mutual relation between phase contrast θ x and intraocular pressure value pre-determines between the phase contrast θ x being obtained by this equipment and the intraocular pressure value of being measured by Goldmann tonometer on can be by experiment arranges.Memorizer 75 storages are used for using probe 10 to measure the program of intraocular pressure, for controlling the program of whole equipment, etc.
In operation part 74, dispose for selecting and automatically with respect to eye E, aim at the auto-alignment pattern of measurement component 4 or manually with respect to eye E, aim at the selector switch 74a of the manual alignment pattern of measurement component 4, for completing of selecting and then to aim at just automatically produce triggering signal with the automatic emission mode that starts to measure or the operating signal generating triggering signal based on switch 5b the selector switch 74b with the manual emission mode that starts to measure, and other.When having selected automatic emission mode, computing and control part 70 each detection signal based on image pick-up device 26 and position sensitive device 58 judges whether alignment is suitable.Based on this result of determination, computing and control part 70 produce to measure and start triggering signal, and the generation based on this triggering signal, and order probe 10 sends ultrasound wave to eye E.
Below explain the operation of the equipment with above structure.First, the person's of being looked into face (head) is fixed on a support unit 2.Scrutineer observes monitor 72 by manipulation stick 5 simultaneously makes equipment aim at the person's of being looked into eye E.At that time, computing and control part 70 show front image and graticule LT and the designator G for aiming at being picked up by image pick-up device 26 on monitor 72, as shown in Fig. 4 A and 4B.
When marking image i1 starts to appear on monitor 72, (when image pick-up device 26 starts certification mark image i1), enables the auto-alignment in X and Y-direction.In addition,, when position sensitive device 58 starts certification mark image i2, enable the auto-alignment in Z direction.The information about the alignment in Z direction that computing and control part 70 detection signal based on from position sensitive device 58 obtains, controls the demonstration of designator G.
Below explain the situation of selecting auto-alignment pattern and automatic emission mode.Computing and control part 70 equipments are at X, Y, and Z direction is with respect to the amount of mis-alignment that is positioned at the eye E of suitable position, and the driving of controlling moving-member 6 is to introduce predetermined permissible range by 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 to measure starting triggering signal to start measure of intraocular pressure.
Below explain the situation of selecting manual alignment pattern and manual emission mode.In this case, scrutineer's manipulation bar 5 (knob 5a) is so that there is (referring to Fig. 4 B) in the form that marking image i1 enters in graticule LT and designator G has aimed at representative being presented on monitor 72.When having completed in each direction, aim at and during by scrutineer's push switch 5b, computing and control part 70 produce to measure and start triggering signals to start measure of intraocular pressure.
And then measure the generation that starts triggering signal, computing and control part 70 make oscillator 11 transmitting ultrasound wave detect from the ultrasound wave of eye E reflection to eye E and by sensor 13.Computing and control part 70 output signal based on specifying part 83 is calculated the intraocular pressure value of eye E and its result is presented on monitor 82.
Use above structure, can easily carry out the aligning between eye E and probe 10.
In above explanation, fixed target light is projected onto in eye E by being formed on the hole 18 at probe 10 center.Needn't be limited to this, also can be configured to the region projection fixed target light of the surrounding of the probe 10 in scioptics 22.The structure of expecting is in this case that for example, use has the diaphragm of the annular aperture of center in optical axis L 2, replaces having the diaphragm 34 in the point-like hole in optical axis L 2.
In above embodiment, alignment mark light is projected onto in eye E by being formed on the hole 18 at probe 10 center.Be not necessarily limited to this, also can be configured to the region projection alignment mark light of the surrounding of the probe 10 in scioptics 22, and the reflected light in the region of the surrounding of the probe 10 in permission image pick-up device 26 detection scioptics 22.The structure that can expect is in this case for example, to use annular light source to replace point source 42.
Fig. 6 is the view that shows the variation of fixed target projection optics system and the first alignment mark projection optics system.In this case, light source 32 (for example, LED) be placed on probe 10 center.
For alignment mark light being projected at a predetermined angle to the first alignment mark projection optics system 140 of observation optical axis L1, be placed on lens 22 outsides.Its reflected light is allowed to pass through the region of the surrounding of the probe 10 in lens 22.In this case, the angle of the optical axis of projection optics system 140 and observation optical axis L1 is determined in case stop sub reflector light becomes by lens 16 interrupts.
At light source 32 as shown in Figure 6, be placed in the situation at probe 10 center, the light source that sends visible ray and infrared light can be usingd as fixed target projection source and alignment mark projection source as light source 32.
In above explanation, it is upper that probe 10 is placed on observation optical axis L1, yet be not limited to this.Probe 10 can be by the direction with perpendicular to optical axis L 1 (X and Y-direction) from observation optical axis L1 displacement, 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 provided as and aims at reference position, and the display position of graticule LT is set, aim at completing place, and other.
Fig. 8 is the structural map of the measuring system of tonometer 100 and the signal of optical system, shows that probe is placed on the situation outside the light path of viewing optical system.
The echo that ultrasonic reflections member (acoustic mirror) 90 reflects from eye E towards sensor 13 from the incidence wave while of oscillator 11 towards eye E reflection.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 eye E.Lens 22 are formed with the hole 22b that allows the ultrasound wave from probe 10 to pass.Incidence wave from oscillator 11 is reflected member 90 reflections to enter eye E through after the 22b of hole.Echo from eye E passes hole 22b, is reflected member 90 reflections, then by sensor 13, is detected.
At lens 22, be placed in the situation between reflecting member 90 and eye E, the lens 22 that form porose 22b in the part corresponding to ultrasonic wave propagation path can avoid the ultrasound wave that may cause in the process of scioptics 22 to weaken.In this case, be coated with and there is the reflecting member 90 stopping from the coating of the catoptrical character of anterior light source 38 and can be used to prevent that anterior reflected light from entering image pick-up device 26 by hole 22b, the noise light preventing thus.
About reflecting member 90, can use the member (for example, transparent in colourless, hard plastic plate) of the character with reflection supersonic wave and transillumination.Even when reflecting member 90 is placed in each light path of projection optics system 30 and projection optics system 40, this also can prevent that fixed target light and alignment mark light from becoming and be interrupted.In the situation that use has the 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 area of the optical path split member of half-reflecting mirror 36 and dichroscope 46.
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 in eye E so that reflecting member 90 is partly 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 light path that reflecting member 90 is placed in projection optics system 30 and 40.
Tonometer can be equipped with in addition for measuring the measurement optical system of the eyes characteristic that is different from intraocular pressure.Fig. 9 shows that ophthalmic refractive power measurement optical system is added to the view of the situation of tonometer.
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 (optical path) of measurement 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 eye E.Reflecting member 90 is placed on before eye E.From the incidence wave of oscillator 11, being reflected member 90 reflects to enter eye E and is reflected member 90 reflections and is detected by sensor 13 from the echo of eye E.So, the intraocular pressure of eye E is measured.
Measure in the transmissive side of dichroscope 301 at rear that optical system 310 is held in place reflecting member 90.Measuring optical system 310 is for projecting the bottom of eye E and receive the catoptrical optical system from bottom by optical pickup apparatus measuring light.Output signal based on 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.
In the reflection side of dichroscope 301, object lens 311 have been placed, dichroscope 312, and completely reflecting mirror 313.In the reflection side of mirror 313, configured the fixed target projection optics system that do not show to make eye E observe fixed target.
In the reflection side of dichroscope 312, configuration be viewing optical system 322, it comprises the imaging len 320 placed with near the relation of the anterior roughly conjugation with eye E and two-dimentional image pick-up device 321.Image pick-up device 321 picks up the front image being formed by light source 325 and the marking image being formed by the alignment mark projection optics system not showing.
By dichroscope 301 make the measurement optical axis L 6 of viewing optical system 322 and optical axis L 7 coaxial.Dichroscope 301 has transmission from the light of measuring the light source of 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 the member with the character of reflection supersonic wave and transillumination (for example, transparent in colourless, hard plastic plate).The measurement 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.
In the structure of Fig. 9, reflecting member 90 is placed on measures optical system 310, viewing optical system 322, and in the shared light path of fixed target projection optics system, but whether be limited to this.This structure only must be by reflecting member 90 reflection from the ultrasound wave of probe 10 with from entering eye E above.For example, reflecting member 90 can be placed between dichroscope 301 and lens 311.
Although more than explain and for example understand ophthalmic refractive power measurement optical system, the invention is not restricted to this and can be applied to for be different from the measurement optical system of the eyes characteristic of intraocular pressure by receiving the reflected light measurement being produced by the measurement light projecting in eye E.For example, non-contact type eyes axial length measure optical system (for example, referring to US 7,434,932 (JP2007-37984A), Cornea thickness survey optical system (for example, referring to JP63-197433 (1988) A), and other can be used.
In addition, can be as required with switch etc., carrying out in response to a triggering signal, carrying out the normal measurement pattern of a measure of intraocular pressure and in response to a triggering signal, between by the continuous measurement pattern of measure of intraocular pressure repeated several times, selecting the pattern of carrying out measure of intraocular pressure that starts triggering signal based on measuring.
Below explain the situation of selecting continuous measurement pattern.And then measure the generation that starts triggering signal, computing and control part 70 order probes 10 continuously send ultrasonic pulse to obtain the information of the variation of the relevant intraocular pressure being caused by the pulsation of eye E to eye E, and carry out the calculation process corresponding to each ultrasonic pulse continuously sending.
Specifically, with within the scope of pulsation period of eye E (for example, within 1.5 seconds) predetermined time interval (for example, 0.1 second interval) ultrasonic pulse is continuously incident in eye E, and calculate the intraocular pressure value corresponding to each ultrasonic pulse.In this way, a lot of intraocular pressure values can be within the pulsation period, obtained and thereby the variation of the intraocular pressure value in the pulsation period can be caught.In this case, each measured value based on obtaining within the pulsation period, can calculate representative value (for example, the meansigma methods of measured value, the central value of measured value) and calculate at the peak of pulsation, the end, and middle measured value.
In above explanation, ultrasonic pulse is for example, to send with predetermined time interval (, 0.1 second interval), yet is not limited to this.Ultrasonic pulse can send with the pre-determined number setting in advance within the pulsation period.Can make about continuously launching the interval of ultrasonic pulse and sending number at random can arranging and can be equipped with its permutator in operation part 74.
In above explanation, in Z direction equipment with respect to the alignment of eye E detected optically (operating distance is detected) but it can be detected by the probe 10 for measure of intraocular pressure.In this case, probe 10 control must be converted for measuring between the control of intraocular pressure and the control for detection of operating distance.In the situation that by utilization 10 operating distances that detect with respect to eye E of popping one's head in, computing and control part 70 are measured and towards eye E, have been sent until the Measuring Time T being detected by sensor 13 from the echo of eye E and thus detection probe 10 are left the operating distance of eye E since the incidence wave of oscillator 11.In other words, since the hyperacoustic of oscillator 11 sent until the Measuring Time T that ultrasound wave is detected by sensor 13 is longer, operating distance is larger.Measuring Time T is shorter, and operating distance is less.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 Z direction is done.
The in the situation that of above structure, for example, computing and control part 70 are controlled probe 10 as controlling probe 10 as the measure of intraocular pressure sensor with respect to eye E with respect to the operating distance sensor of eye E and after aligning completes before aligning completes.This can simplify the structure about the alignment in Z direction of eye E for detection of equipment.
Do above explanation and determine intraocular pressure with the difference of the acoustic impedance of the phase contrast generation based on between input phase and output phase.The invention is not restricted to this and can be applied to can be by carrying out from the comparison of the incidence wave of oscillator 11 and the echo that detected by sensor 13 and the structure that calculation process is determined intraocular pressure.For example, it can be configured to by carrying out determining intraocular pressure from comparison and the calculation process of the incident wave frequency of oscillator 11 and the reflection wave frequency that detected by sensor 13.Specifically, can be equipped with phase-shift circuit changes the hyperacoustic frequency being produced by oscillator 11 when there is phase contrast between the input oscillogram by when to oscillator 11 and the output waveform from sensor 13 phase contrast is moved to zero.Intraocular pressure is by detection, to work as the frequency variation of phase contrast while being moved to zero to determine.
Claims (6)
1. a non-contact ultrasonic tonometer, for by utilizing ultrasound wave with the intraocular pressure of the non-contact mode measuring person's of being looked into eyes, is characterized in that, described tonometer comprises:
Comprise for make described ultrasound wave be incident on described in oscillator on the person's of being looked into eyes and for detection of the probe of described hyperacoustic sensor of the eye reflections from the described person of being looked into; And
For the anterior viewing optical system of observing described eyes,
Wherein said probe is placed on the optical axis of described viewing optical system, and the described optical axis of the axis of described probe and described viewing optical system is coaxial, and
Described viewing optical system forms the image of described front portion by the peripheral region of described probe.
2. tonometer as claimed in claim 1, is characterized in that,
Described viewing optical system comprises image pick-up device and for form the object lens of described front image on described image pick-up device, and
Described object lens have hole, insert described probe in described hole.
3. tonometer as claimed in claim 1, is characterized in that,
Described viewing optical system comprises image pick-up device and for form the object lens of described front image on described image pick-up device, and
Described object lens are placed on described probe before and have the hole that allows described ultrasound wave to pass through.
4. tonometer as claimed in claim 1, is characterized in that, further comprise and being equipped with for fixed target being projected on 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 allows the fixed target light from described light source to be passed.
5. tonometer as claimed in claim 1, is characterized in that, comprise further and being equipped with for alignment mark being projected to the alignment mark projection optics system of the light source of the alignment mark projection on described eyes, and
The alignment mark detection optical system of the image pick-up device that detects the corneal reflex image being formed 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.
6. tonometer as claimed in claim 5, is characterized in that,
Described probe has the hole that allows the alignment mark light from described light source to pass through.
Applications Claiming Priority (6)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2008120793 | 2008-05-03 | ||
| JP2008120794 | 2008-05-03 | ||
| JP2008120794A JP5117275B2 (en) | 2008-05-03 | 2008-05-03 | Non-contact ultrasonic tonometer |
| JP2008-120793 | 2008-05-03 | ||
| JP2008120793A JP5410692B2 (en) | 2008-05-03 | 2008-05-03 | Non-contact ultrasonic tonometer |
| JP2008-120794 | 2008-05-03 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN101569545A CN101569545A (en) | 2009-11-04 |
| CN101569545B true CN101569545B (en) | 2014-03-19 |
Family
ID=41229129
Family Applications (1)
| 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) |
Families Citing this family (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP5562703B2 (en) * | 2010-03-31 | 2014-07-30 | 株式会社ニデック | Non-contact ultrasonic tonometer |
| WO2015110866A1 (en) | 2014-01-22 | 2015-07-30 | Analogic Corporation | Imaging apparatus and interventional instrument event mapper |
| 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 |
| CA2979687A1 (en) | 2015-03-16 | 2016-09-22 | Nicole Elizabeth SAMEC | Methods and systems for diagnosing and treating health ailments |
| AU2017246901B2 (en) | 2016-04-08 | 2022-06-02 | Magic Leap, Inc. | 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 |
| JP7158395B2 (en) | 2017-02-23 | 2022-10-21 | マジック リープ， インコーポレイテッド | Variable focus imaging device based on polarization conversion |
| EP3638097A1 (en) | 2017-06-13 | 2020-04-22 | 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 |
| JP7210851B2 (en) | 2018-09-28 | 2023-01-24 | 株式会社ニデック | Ultrasonic tonometer and ultrasonic actuator |
| WO2020065388A1 (en) | 2018-09-28 | 2020-04-02 | Nidek Co., Ltd. | 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 |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5975698A (en) * | 1997-10-09 | 1999-11-02 | Kabushiki Kaisha Topcon | Ophthalmic instrument |
| EP1327412B1 (en) * | 2002-01-10 | 2007-08-15 | Carl Zeiss Meditec AG | Apparatus for illuminating the lens of a human eye |
| CN101065054A (en) * | 2004-07-14 | 2007-10-31 | e动太平股份有限公司 | Improved apparatus and method of intraocular pressure determination |
Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| 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 |
| JPH04114626A (en) * | 1990-09-04 | 1992-04-15 | Canon Inc | Ophthalmologic apparatus |
| JPH04114625A (en) * | 1990-09-04 | 1992-04-15 | Canon Inc | Ophthalmological apparatus |
| JPH05253190A (en) * | 1991-10-10 | 1993-10-05 | Massie Res Lab Inc | Non-contact type tonometer |
| JP4126249B2 (en) * | 2003-05-30 | 2008-07-30 | 株式会社ニデック | Ophthalmic equipment |
| WO2008072527A1 (en) * | 2006-12-08 | 2008-06-19 | Nihon University | Intraocular pressure measuring device |
-
2008
- 2008-05-03 JP JP2008120793A patent/JP5410692B2/en not_active Expired - Fee Related
-
2009
- 2009-04-30 CN CN200910140516.5A patent/CN101569545B/en not_active Expired - Fee Related
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5975698A (en) * | 1997-10-09 | 1999-11-02 | Kabushiki Kaisha Topcon | Ophthalmic instrument |
| EP1327412B1 (en) * | 2002-01-10 | 2007-08-15 | Carl Zeiss Meditec AG | Apparatus for illuminating the lens of a human eye |
| CN101065054A (en) * | 2004-07-14 | 2007-10-31 | e动太平股份有限公司 | Improved apparatus and method of intraocular pressure determination |
Non-Patent Citations (1)
| Title |
|---|
| JP特开平11-113846A 1999.04.27 |
Also Published As
| Publication number | Publication date |
|---|---|
| CN101569545A (en) | 2009-11-04 |
| JP5410692B2 (en) | 2014-02-05 |
| JP2009268651A (en) | 2009-11-19 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101569545B (en) | Non-contact ultrasonic tonometer | |
| EP2113192B1 (en) | Non-contact ultrasonic tonometer | |
| USRE45013E1 (en) | Non-contact ultrasonic tonometer | |
| US8016418B2 (en) | Eye axial length measurement apparatus | |
| AU2017357045B2 (en) | Optical coherence tomography systems and methods with dispersion compensation | |
| EP3743679B1 (en) | Methods and systems of optical coherence tomography with fiducial signal for correcting scanning laser nonlinearity | |
| JP2004313758A (en) | Ophthalmic apparatus | |
| JP5201852B2 (en) | Ophthalmic equipment | |
| CN101467874A (en) | Ophthalmologic apparatus | |
| CN108024708A (en) | Method and arrangement for eyes measurement | |
| JP2015008955A (en) | Non-contact ultrasonic tonometer | |
| JP5397670B2 (en) | Non-contact ultrasonic tonometer | |
| JP2011045602A (en) | Non-contact ultrasonic tonometer | |
| JP5117275B2 (en) | Non-contact ultrasonic tonometer | |
| JP5601622B2 (en) | Non-contact ultrasonic tonometer | |
| EP2260765A1 (en) | Non-contact ultrasonic measurement device | |
| JP5465946B2 (en) | Non-contact ultrasonic tonometer | |
| JP5410923B2 (en) | Non-contact ultrasonic tonometer | |
| JP2003111729A (en) | Method and instrument for measuring ocular optical property | |
| JPH0531073A (en) | Ophthalmological measuring device | |
| JPH03111027A (en) | Dimension measuring instrument for living body eye | |
| JPH0191832A (en) | Ophthalmic measuring apparatus | |
| JPH01300922A (en) | Opthalmic measuring apparatus |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20140319 Termination date: 20160430 |