JP3387599B2 - Fundus blood flow meter - Google Patents

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a fundus blood flow meter for measuring blood flow in blood vessels on the fundus of an eye to be examined.

[0002]

2. Description of the Related Art FIG. 4 shows a conventional example of a fundus blood flow meter, which is a modification of a slit lamp generally used in ophthalmology. An illumination optical system is arranged on the optical path K1, and the white light flux from the illumination light source 1 is reflected by the perforated mirror 2 to cancel the refracting power of the slit 3, the lens 4 and the cornea of the eye E to be examined. The blood vessel Ev on the fundus oculi Ea is illuminated via the contact lens 5 that allows observation of Ea. Further, on the optical path behind the perforated mirror 2, a measurement laser light source 6 that emits He-Ne laser light for measurement is arranged, and the measurement light from the measurement laser light source 6 is emitted from the perforated mirror 2. It passes through the central opening and is made coaxial with the light flux from the illumination light source 1, and irradiates the fundus Ea in a spot shape.

The blood cells flowing in the blood vessel Ev and the light flux scattered and reflected by the blood vessel wall are objective lenses 7a, 7 of the stereoscopic light receiving optical system arranged on the optical paths K2, K3 forming the angle α '.
b, and is reflected by the mirrors 8a and 8b and the mirrors 9a and 9b, and is observed by the examiner as a fundus image through the eyepieces 10a and 10b.
Select the measurement site while observing the fundus Ea while looking through.

FIG. 5 is a fundus image observed by an examiner, and a blood vessel Ev to be measured is prepared in advance on the focal planes of the eyepieces 10a and 10b in the region I illuminated by the illumination light. When the axis SC is aligned with the scale SC, the measurement light from the measurement laser light source 6 and the blood vessel Ev are aligned, and the measurement site is determined by the spot light flux PS from the measurement laser light source 6. At this time, the reflected light flux from the fundus Ea due to the measurement light is received by the photomultipliers 12a and 12b via the optical fibers 11a and 11b.

The received light signal contains a predetermined beat signal component generated by the interference of the component Doppler-shifted by the blood flow in the blood vessel Ev and the component reflected by the stationary blood vessel wall. , The frequency of this beat signal is analyzed to obtain the blood flow velocity in the blood vessel Ev.

FIG. 6 shows photomultipliers 12a and 12a.
It is an example of the result of frequency analysis of the received light signal measured in b, the horizontal axis shows the frequency Δf, and the vertical axis shows the output ΔS. The relationship between the maximum frequency shift Δfmax, the wave number vector κi of the incident light beam and the wave number vector κs of the received light beam, and the velocity vector υ of the blood flow can be expressed as Δfmax = (κs −κi) ・ υ… (1) it can.

Therefore, the photomultipliers 12a, 1
2b, maximum shifts Δfmax1 and Δfmax2 of the frequency calculated from the respective received light signals, the wavelength λ of the laser light,
Using the refractive index n of the measurement site, the angle α formed by the light receiving optical axes K2 and K3 in the eye, and the angle β formed by the plane formed by the light receiving optical axes K2 and K3 in the eye and the velocity vector υ of the blood flow. By modifying the equation (1), the maximum velocity Vmax of blood flow can be expressed as Vmax = {λ / (nα)} · | Δfmax1−Δfmax2 | / cosβ ... (2).

As described above, by performing the measurement in two directions, the contributions of the measurement light in the incident direction are canceled out, and the blood flow in an arbitrary region on the fundus Ea can be measured.

Further, from the relationship between the intersection line A between the plane formed by the two light receiving optical paths K2 and K3 and the fundus Ea and the angle β formed by this intersection line A and the velocity vector υ of the blood flow, the true blood is obtained. In order to measure the flow velocity, it is necessary to set β = 0 ° in the equation (2) and match the intersection line A with the velocity vector υ. Therefore, in the conventional example, the entire light receiving optical system is rotated, or an image rotator is arranged in the light receiving optical system so as to be optically matched.

[0010]

However, in the above-mentioned conventional example, the maximum value Δfmax of the Doppler shift is detected as an interference signal between the component shifted by the blood flow and the stationary blood vessel wall. The maximum shift Δfmax obtained is the lack of code information | Δfmax |.

Therefore, when measuring blood flow in blood vessels at different parts of the fundus Ea, maximum frequency shifts Δfmax1 and Δfmax1
There are cases where the signs of fmax2 are both positive, both negative, and different signs. Therefore, depending on the region to be measured, there arises a problem that it becomes impossible to determine the maximum blood flow velocity Vmax by the equation (2).

This problem will be described with reference to FIG.
In FIG. 4, assuming that the signal light is incident from the center hi = 0 of the pupil Ep and the scattered light is received from the predetermined portions hs1 and hs2 of the pupil Ep, the angles at which the hs1 and hs2 are seen from the fundus Ea are as shown in FIG. It is an angle α formed by the light receiving optical axis.

Now, considering the case where the blood vessel Ev1 in the center of the fundus Ea and the blood vessel Ev2 in the periphery are measured, when measuring the blood vessel Ev1, the maximum frequency obtained by the received light signal from the direction of the site hs1 is considered. The shift Δfmax1 and the maximum frequency shift Δ obtained from the received light signal from the direction of the part hs2
It has a different sign from fmax2. In this case, the signal light is the blood vessel Ev.
Since it is vertically incident on 1, there is no frequency shift caused by the direction of the signal light, and the obtained frequency shift is only that caused by the direction of observation. Where the blood vessel Ev1
Considering the velocity vector υ1 of the blood flow of and the wave vector κs1 in the hs1 direction and the wave vector κs2 in the hs2 direction, since they exist in different directions with respect to the perpendicular of the velocity vector υ1, their inner products have different signs. A frequency shift with a different sign is occurring.

On the other hand, when measuring the blood vessel Ev2 in the peripheral region, the regular reflection light κi 'having a frequency shift of 0 is
Since there are hs1 and hs2 directions in the same direction, the frequency shift of the same sign is occurring. here,
A straight line connecting the center Eo of the fundus Ea and the blood vessel Ev2, that is, the fundus Ea
The angle between the normal of the blood vessel Ev2 and the direction of the wavenumber vector κi of the signal light is φi, the angle φc with respect to the perpendicular and the wavenumber vector indicating the specular reflection light of the vector κi facing in the opposite direction of the vector κi is κi. 'Is.

The object of the present invention is to solve the above-mentioned problems,
By providing an incident direction switching means for switching the incident direction of the measurement light, it is possible to provide a fundus blood flow meter that detects the above-mentioned code determination region and can always perform correct measurement regardless of the site or direction of the fundus blood vessel. is there.

[0016]

Means for Solving the Problems A fundus blood flow meter according to the present invention for achieving the above object comprises a measuring light irradiation means for irradiating a blood vessel on the fundus of an eye to be measured with coherent measuring light, and the measurement. Light receiving means for receiving the signal light in which the light is scattered by the intravascular particles and the reference light scattered from the blood vessel wall from two different directions, and the respective output signals of the light receiving means are subjected to frequency analysis to detect the respective Doppler shifts. Signal processing means for
And an incident direction switching means for switching the incident direction of the measurement light to the fundus with respect to the light receiving direction of the light receiving means, and an arithmetic means for calculating the blood flow velocity in the blood vessel based on the output of the signal processing means. Comparing means for comparing the Doppler shifts obtained from the measuring light in different incident directions before and after switching by the switching means, and the computing means by using data from the incident direction that can be correctly measured based on the output of the comparing means. And a control means for controlling so as to perform blood flow measurement. Further, the fundus blood flow meter according to the present invention,
Measuring light irradiating means for irradiating a blood vessel on the fundus of the eye to be inspected with coherent measuring light, and signal light for scattering the measuring light by intravascular particles and reference light for scattering from the blood vessel wall from two different directions. Light receiving means, signal processing means for frequency-analyzing respective output signals of the light receiving means to detect respective Doppler shifts, and computing means for calculating blood flow velocity in a blood vessel based on the output of the signal processing means. Incident direction switching means for switching the direction of incidence of the measuring light on the fundus with respect to the light receiving direction of the light receiving means, and Doppler obtained from the measuring light of different incident directions before and after switching by the switching means. It is characterized by comprising a comparison means for comparing shifts and a control means for controlling the calculation means so as to obtain a correct blood flow value from the measurement data based on the output of the comparison means.

[0017]

The fundus blood flow meter having the above-described structure irradiates the fundus blood vessel with coherent measurement light, receives scattered light from the intravascular particles and the blood vessel wall from two directions, and shifts the Doppler shift due to blood flow. When detecting and calculating the blood flow velocity in the blood vessel, the results of the blood flow velocity measured by switching the incident direction of the measurement light are compared to avoid the problem of the inversion of the sign of the measurement signal.

[0018]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described in detail with reference to the embodiments shown in FIGS. FIG. 1 is a configuration diagram of a fundus blood flow meter in the present embodiment, in which only a light flux in a yellow-green range is transmitted on an optical path from an illumination light source 21 including a tungsten lamp that emits white light to an objective lens 22. Bandpass filter 23, condenser lens 24, mirror 25, field lens 26, ring slit 27, relay lens 2
8, 29, perforated mirror 30, image rotator 31
Are arranged. In addition, a light receiving optical system 35 in which a pair of small mirrors 32a and 32b, lenses 33a and 33b, and photomultipliers 34a and 34b are arranged on the optical path extending upward in two directions from the opening of the perforated mirror 30.
Is provided. In FIG. 1, in order to avoid duplication, the small mirror 32a among the small mirror pairs 32a and 32b is used.
Only the members on the optical axis of are shown.

An image stabilizer 36 is arranged on the optical path behind the perforated mirror 30, and lenses 37 and 38, galvanometric mirrors 39, lenses 40 and 41, and galvanometric mirror 42 are sequentially arranged in the image stabilizer 36. It is provided in. The galvanometric mirrors 39 and 42 are made rotatable by the operating rod 43, and the galvanometric mirror 39 rotates about a rotation axis perpendicular to the paper surface.
Rotates about an axis of rotation that is parallel to the plane of the paper that is orthogonal to this axis of rotation.

A focusing lens 45, a lens 46, and a dichroic mirror 47, which are movable along the optical axis, are arranged on the optical path behind the galvanometric mirror 42, and a half mirror is provided on the optical path in the reflection direction of the dichroic mirror 47. 48, lens 49, TV camera 50
Are arranged to form an observation optical system 52, and the output of the television camera 50 is connected to the television monitor 51. A mirror 53, a lens 54, a filter 55, and a one-dimensional CCD array sensor 56 with an image intensifier are arranged on the optical path in the reflection direction of the half mirror 48 to form a blood vessel detection system 57. The dichroic mirror 47 is the galvanometric mirror 39, 4.
It is conjugated with 2.

On the passing side of the dichroic mirror 47,
A lens 59, an aperture 60 at a position conjugate with the fundus Ea of the eye E to be inspected, an imaging lens 61, and a measurement laser optical system that emits laser light as signal light are arranged.
The measurement laser optical system includes an aperture 62 with two holes, and a fixed mirror 6 arranged behind one hole of the aperture 62.
3, an optical path switching mirror 64 arranged behind the other hole of the aperture 62, and a measurement laser light source 65 arranged behind the switching mirror 64. The two-hole aperture 62 is a dichroic mirror 47, Eye E
The pupil and the two galvanometric mirrors 39 and 42 are substantially conjugate with each other.

The output of the CCD array sensor 56 is connected to a control circuit 66. The control circuit 66 has a blood vessel image analysis circuit composed of a tuning storage circuit, a memory processing circuit, a control unit, etc., and its output. Is a galvanometric mirror 3
9 is connected. The output from the system control section 67 is connected to the control circuit 66, and the output of the system control section 67 is also connected to the mirror driving means 68 for driving the optical path switching mirror 64. Also, photo multiplier 3
The outputs of 4a and 34b are connected to the system control unit 67.

FIG. 2 shows the arrangement of the respective luminous fluxes with respect to the pupil of the eye E to be examined, the image 27 'of the ring slit 27 shows the position of the entire luminous flux of the illumination of the fundus Ea, and the images 32a'32b' of the small mirror pairs 32a, 32b. Indicates the received light beam position of the Doppler signal, and images 62a 'and 62b' of the two openings 62a and 62b of the aperture 62 with two holes of the measurement laser optical system indicate the incident light beam position of the laser light which is the signal light. There is.
The aperture image 30 'of the perforated mirror 30 and the image 47' of the dichroic mirror 47 show the observation light beam position.

The illumination luminous flux from the illumination light source 21 is a bandpass filter 23, a condenser lens 24, and a mirror 2.
5. After passing through the field lens 26, the ring slit 27
After being imaged at the aperture of the eye, and again after being imaged again by the perforated mirror 30 by the relay lenses 28 and 29, the image passes through the image rotator 31 and the objective lens 22 and becomes a slit ring image 27 'on the pupil of the eye E to be inspected. An image is formed, and the fundus Ea is illuminated almost uniformly.

The light reflected by the fundus Ea is extracted from the aperture image 30 'of the perforated mirror 30 in the pupil, and returns to the same optical path through the aperture of the perforated mirror 30 to the lenses 37 and 38 of the image stabilizer 36 and the galvanometer. The light passes through the metric mirror 39, the lenses 40 and 41, and the galvanometric mirror 42, further passes through the focusing lens 45 and the lens 46, is reflected by the dichroic mirror 47, and passes through the half mirror 48 and the lens 49 to the television camera 50 as a fundus image Ea ′. An image is formed and displayed on the television monitor 51. The examiner performs alignment of the device and selection of a measurement site while observing the television monitor 51.

Further, the light flux reflected by the half mirror 48 passes through the mirror 53, the lens 54 and the filter 55 of the blood vessel detection system 57, and at the CCD array sensor 56, the fundus image Ea 'captured by the television camera 50. The light is received as an enlarged blood vessel image Ev '. CCD array sensor 56
In the blood vessel image analysis circuit in the control circuit 66, the output signal from is processed into data representing the movement amount of the blood vessel Ev, and then the galvanometric mirror 39 drives and controls so as to compensate the movement amount by the control circuit 66. To be done.

On the other hand, the signal light from the measuring laser light source 65 has the optical path switching mirror 64 deviated from the optical path.
After passing through one hole 62a of the two-hole aperture 62, it passes through the aperture 60 that specifies the measurement site by the imaging lens 61, and then returns to the above-mentioned optical path in the reverse direction, and the beam on the pupil 2 through the objective lens 22. Aperture 6 with holes
The light flux position is specified by the second opening image 62a ′, and the light is projected onto the blood vessel Ev on the fundus Ea of the eye E to be examined.

The opening 62 of the aperture 62 with two holes
a and 62b are the dichroic mirror 4 at the conjugate position.
Since the image is formed outside the image 47 ′ of No. 7, the signal light is not eclipsed by the dichroic mirror 47, and the reflected light flux from the blood vessel Ev returns through the same optical path, and a part of it is reflected by the small mirror pair 3
It is reflected in two directions by 2a and 32b. Small mirror pair 3
The light fluxes reflected by 2a and 32b are light fluxes extracted from the mirror images 32a 'and 32b' on the pupil, and are focused on the photomultipliers 34a and 34b via the lenses 33a and 33b. This received light signal is sent to the system control unit 67 for measuring the flow velocity, and frequency analysis is performed as in the conventional example.

On the other hand, the light beam which is not reflected by the pair of small mirrors 32a and 32b is the light beam extracted from the aperture image 30 'on the pupil, and is formed by the aperture of the perforated mirror 30, the image stabilizer 36, the focusing lens 45 and the lens 46. As described above, a part of the light is reflected by the dichroic mirror 47, passes through the half mirror 48 and the lens 49, and is formed as a spot image by the TV camera 50.
Is displayed together with the fundus image Ea 'by the illumination light source 21 and acts as an index of the measurement site.

The fundus generated by the measuring laser light source 65
The reflected light flux at Ea enters the blood vessel detection system 57 via the half mirror 48, but since the filter 55 blocks the wavelength of the measurement laser light source 65, the CCD array sensor 56 causes the blood vessel image Ev ′ by the illumination light source 21. Only the image will be taken.

The measuring light from the measuring laser light source 65 is
An image is formed on the focal plane of the aperture 60 that is conjugate with the fundus Ea of the eye E to be inspected by the imaging lens 61, and the conjugate relationship is adjusted by the focusing lens 45. Therefore, when the examiner operates a focus knob (not shown) to perform focusing, the focusing lens 45 moves along the optical axis,
The image pickup surface of the television camera 50, the image pickup surface of the CCD array sensor 56, and the focal plane of the aperture 60 of the lens 61 are simultaneously conjugated with the fundus oculi Ea, and the spot image PS is also focused together with the fundus oculi image Ea ′.

At this time, a fundus image Ea 'is displayed on the television monitor 51 as shown in FIG. Spot image above
Since the PS is fixed at the center of the visual field, the spot to be measured is selected by the operation rod 43 so that the spot image PS coincides with the predetermined measurement region, the image rotator 31 is rotated, and the blood vessel image Ev ′ to be measured is set as the axis. Align with A. The direction of the coordinate axis A is the plane connecting the centers of the small mirror pairs 32a and 32b to the fundus Ea.
The direction of the line of intersection with is shown, and it is displayed on the television monitor 51 as an index for adjusting the image rotator 31. When the examiner rotates the image rotator 31, the fundus image Ea ′ of the eye E to be examined rotates as indicated by an arrow C.

Then, the blood vessel Ev and the axis A are made to coincide with each other, and FIG.
By setting β = 0 ° in, the following advantages (a) to (c) can be obtained.

(B) From equation (2), β = 90 °, that is, cos β = 0
, The maximum frequency shift Δfmax1 and Δfmax
Although it becomes impossible to obtain the absolute value of the maximum blood flow velocity Vmax from 2, it is possible to avoid an unmeasurable position by rotating the fundus image Ea ′ so that β = 0 °.

(B) Since it is not necessary to measure the angle β, error factors are reduced and the work is simplified.

(C) As described in the conventional example, the blood flow velocity is obtained from the interference signal between the scattered and reflected light from the blood vessel wall and the scattered and reflected light in blood, so that the fundus Ea is measured in the direction of the axis A during measurement. Even if the blood vessel moves, the measurement result is not affected if the blood vessel Ev is made substantially parallel to the axis A direction.

On the other hand, when the fundus Ea moves in the axial direction orthogonal to the axis A, the signal light from the measurement laser light source 65 deviates from the blood vessel Ev at the measurement site and the measured value becomes unstable. In this case, since the movement amount of the blood vessel Ev needs to be detected only in that direction, in this embodiment, the blood vessel detection system 57 and the image stabilizer 36 perform tracking in only that direction.

In this tracking, the CCD for detecting the moving amount of the blood vessel image Ev ′ is used in order to measure the blood flow velocity accurately and promptly for any blood vessel Ev to be examined.
The array sensor 56 may be arranged perpendicularly to the blood vessel image Ev ′ to be measured, and by setting β = 0 °, there is an advantage that it is not necessary to use a two-dimensional sensor.

In this embodiment, CC is applied in the direction orthogonal to the axis A.
When the elements of the D array sensor 56 are arranged and the selection of the measurement site is completed as shown in FIG. 3, the CCD array sensor 56 of the blood vessel detection system 57 has a rod shape in a direction orthogonal to the axis A. The fundus oculi image Ea ′ represented by the region I of FIG.

After the alignment is completed in this way,
When the examiner presses a measurement switch (not shown) to start the measurement, the system control unit 67 receives this signal and issues a tracking start command to the control circuit 66. At the same time, the signals of the photomultipliers 34a and 34b are taken into the system control unit 67, and first, the aperture 6 on the pupil of the eye E to be examined.
The maximum frequency shifts | Δfmax1 | and | Δfmax2 | due to the signal light incident from the position of the second aperture image 62a ′ are obtained. And | Δfmax1 | is the photomultiplier 3
4a is the processing result of the output signal, and | Δfmax2 | is the processing result of the output signal from the photomultiplier 34b.

Here, the incident signal light is the aperture image 62.
Since it is located at a ′ and is provided at a position in the same direction with respect to the received light beam positions 32a ′ and 32b ′, normally the maximum velocity Vmax is set to cosβ = 1 in equation (2), and Vmax = {λ
/ (Nα)} · || Δfmax1 | − | Δfmax2 ||, but the true flow velocity is Vmax =
There are also cases where {λ / (n / α)} · || Δfmax1 | + | Δfmax2 || must be set. In this embodiment, first, as a temporary measurement, in this state, the maximum speed Vm according to the above equation (2) is
After calculating ax, the optical path switching mirror 64 is inserted into the optical path by the output of the system control unit 67, and the signal light is made incident through the other one opening 62b of the aperture 62 with two holes for measurement.

As shown in FIG. 2, the opening image 62b 'formed on the pupil of the eye E by the opening 62b passes through the center of the other opening image 62a', and the image of the small mirror pair 32a, 32b. It is arranged so as to have its center on a straight line parallel to the straight line connecting the centers of 32a 'and 32b'. In particular, in this embodiment, the interval is larger than the distance between the centers of the images 32a 'and 32b', and two The straight line connecting the midpoints of the straight lines is selected so as to be orthogonal to the straight line connecting the respective centers.

After switching the incident light beam position from the aperture image 62a 'of the aperture 62 to the aperture image 62b' thus selected, the system controller 67 again takes in signals from the two photomultipliers 34a and 34b, The maximum frequency shifts | Δfmax1 '| and | Δfmax2' | are calculated, and the maximum velocity Vmax is calculated according to equation (2). If the maximum velocity Vmax at this time is Vmax ', the incident light flux is as described above. Maximum frequency shift | Δfmax
The area of the angle φi in FIG. 7 where the signs of 1 | and | Δfmax2 | are switched, and the maximum frequency shifts | Δfmax1 '| and | Δfmax2' |
It is possible to separate the areas where the signs of and are switched.
In the area where the signs are not changed, Vmax≈Vmax '. Further, in the area where one of the maximum speeds Vmax and Vmax 'is switched, it is possible to create the relationship (the side where the code is not switched)> (the side where the code is switched).

Therefore, in the apparatus of this embodiment, the system control unit 67 compares the two maximum velocities Vmax and Vmax 'to determine the appropriate incident direction of the signal light for obtaining the true maximum flow velocity. can do. Based on this information, the system control unit 67 controls the optical path switching mirror 64 to an appropriate state so as to perform the main measurement. In the main measurement, the maximum velocity Vmax or Vmax ′ is measured at an appropriate time interval.
The calculation is repeated and continuous measurement is performed.

In this embodiment, the maximum speeds Vmax and Vma
Although a method of determining x'before the main measurement was shown, instead of this, the maximum speed Vmax, Vmax 'is measured and calculated before the main measurement, and then the presence or absence of the sign inversion is checked. It is also possible to use software to reverse the sign of the operation in equation (2).

[0046]

As described above, in the fundus blood flow meter according to the present invention, when detecting the Doppler shift caused by the fundus blood flow from two directions, the incident direction of the measurement light is switched to measure the blood flow velocity. It is possible to avoid the problem of the sign inversion of the measurement signal by carrying out and comparing the respective measurement results. As a result, the correct blood flow velocity can be always measured for blood vessels existing in any position and in any direction within the eyeball.

[Brief description of drawings]

FIG. 1 is a configuration diagram of a present embodiment.

FIG. 2 is an explanatory diagram of a light flux arrangement on a pupil.

FIG. 3 is an explanatory diagram of an observation fundus image.

FIG. 4 is a configuration diagram of a conventional example.

FIG. 5 is an explanatory diagram of an observation fundus image.

FIG. 6 is a graph showing a frequency distribution of a received light signal.

FIG. 7 is an explanatory diagram of an arrangement of an intraocular light beam.

[Explanation of symbols]

1,21 Illumination light source 2, 30 perforated mirror 22 Objective lens 31 Rotator 36 Image stabilizer 52 Observation optical system 57 Blood vessel detection system 62 2-hole aperture 64 optical path switching mirror 65 Laser light source for measurement 66 System control unit

Claims (2)

(57) [Claims] 1. A measurement light irradiating means for irradiating a blood vessel on the fundus of an eye to be inspected with coherent measurement light, and a signal light for scattering the measurement light by intravascular particles and a reference light scattered from a blood vessel wall. Light receiving means for receiving light from two different directions, signal processing means for performing frequency analysis on respective output signals of the light receiving means to detect respective Doppler shifts, and blood flow velocity in a blood vessel based on the output of the signal processing means. and a calculating means for calculating an incident direction switching means for switching respect receiving direction of the light receiving means an incident direction of the fundus of the measurement light, switching Ru said measurement before and after different incident directions by said changeover switching means Comparing means for comparing the Doppler shifts obtained from light, and incidence that can be correctly measured based on the output of the comparing means
Determine the direction and use the data from the incident direction to measure the blood flow.
Fundus blood flow meter, characterized in that a control means for controlling so as to perform constant. 2. A measuring light which is coherent with a blood vessel on the fundus of an eye to be examined.
And a measuring light irradiating means for irradiating the
Signal light scattered by and reference scattered from the vessel wall
Light receiving means for receiving light from two different directions, and the light receiving means
Frequency analysis of each output signal of
Signal processing means for detecting plastic shift and the signal processing means
Calculating means for calculating the blood flow velocity in the blood vessel based on the output of
The direction of incidence of the measurement light on the fundus of the eye.
Incident direction switching means for switching the light receiving direction of the step,
The measurement of different incident directions before and after switching by the switching means
Comparison means for comparing Doppler shifts obtained from constant light
And correct from the measured data based on the output of the comparison means.
A control means for controlling the arithmetic means so as to obtain a blood flow value
A fundus blood flow meter comprising: