JP4585814B2 - Ophthalmic equipment - Google Patents

Description

  The present invention relates to an ophthalmologic apparatus, and more particularly to an ophthalmologic apparatus for performing ophthalmologic diagnosis by photographing or measuring an eye to be examined.

  There is an ophthalmologic apparatus for photographing or measuring the fundus or the eye for a predetermined time for ophthalmologic diagnosis. For example, a fundus camera for photographing an infrared fluorescent image of the fundus is known, and an ophthalmologic measurement device for measuring the anterior ocular protein concentration is known (Patent Document 1). An ophthalmologic photographing apparatus is also known (Patent Document 2).

In the case of such an apparatus for photographing or measuring the eye to be examined, if the line-of-sight direction of the eye to be examined is not stable, the photographing / measuring location moves greatly, and a desired result cannot be obtained. Therefore, the direction of the line of sight is stabilized by allowing the subject to keep watching the fixation lamp (fixation target). However, since blinking and poor fixation occur inevitably, the line of sight is always stabilized. Has its limits. Therefore, techniques for detecting the occurrence of fixation disparity and performing shooting and measurement smoothly have been proposed (Patent Documents 3 and 4).
JP-A-2-82938 Japanese Patent Laid-Open No. 1-204643 Japanese Patent Laid-Open No. 10-14878 JP-A-62-286432

  However, the conventional technique for detecting the fixation state is to detect fixation disparity when performing instantaneous measurement multiple times, such as a non-contact tonometer, so when a fixation disparity is detected, simply start measurement. Ophthalmology that prohibits (Patent Document 3) or prompts the subject to fixate when a fixation failure occurs (Patent Document 4), and continuously measures (photographs) within a continuous time It cannot be applied to the device. Accordingly, there has been a problem that in an apparatus in which photographing or measurement results are continuous in time, when fixation failure occurs, photographing or measurement must be repeated.

  The present invention has been made in order to solve such problems, and can continuously monitor the fixation state of the eye to be inspected. It is an object of the present invention to provide an ophthalmologic apparatus that enables ophthalmologic photographing or ophthalmic measurement.

The present invention
Eye information acquisition means for acquiring eye information;
Fixation position detection means for continuously detecting the fixation position of the eye to be examined;
Arithmetic means for correcting eye information based on fixation information obtained by continuously detecting fixation positions;
In an ophthalmic device having
The subject eye information acquisition means is means for acquiring continuous partial image data by scanning the fundus,
When the fixation disparity is detected, the arithmetic means corrects the partial image data obtained at that time and combines the partial image data to form one fundus examination eye image .

  The eye information acquisition means is a measuring means for measuring the anterior aqueous humor protein concentration, an imaging means for taking an infrared fluorescent image of the fundus, or acquiring a continuous slit-shaped partial image by scanning the fundus. The fixation position detection means detects the fixation position from the light amount distribution of the image picked up by the anterior eye part or the fundus moving image pickup means. The calculation means calculates by excluding the measured protein concentration according to fixation disparity, corrects the position of the fundus infrared fluorescence image, or corrects the partial image when fixation disparity is detected ( Complement) to form one fundus image.

  In the present invention, in addition to the means for acquiring original eye information by photographing or measurement, the fixation position information of the eye to be examined is continuously captured by photographing the fundus or anterior eye portion, thereby causing fixation disparity or fixation. The captured image or the measured value is corrected based on the movement. Therefore, even if measurement or imaging is performed that is longer than the fixation time limit of the eye to be inspected and fixation errors such as fixation disparity occur during that time, high-quality measurement results or imaging can be performed without interrupting measurement or imaging. An image can be obtained.

  The present invention includes eye information acquisition means for acquiring eye information and fixation position detection means for continuously detecting the fixation position of the eye, and the eye to be examined based on the obtained fixation information A subject eye information acquisition means for correcting information and acquiring subject eye information is a measurement means (Example 1) for measuring the anterior ocular aqueous humor protein concentration, and an imaging means for taking an infrared fluorescent image of the fundus. (Embodiment 2) Or, as a means (Example 3) for acquiring a continuous slit-shaped partial image by scanning the fundus, the light amount distribution of the image captured by the anterior eye part or the fundus moving image capturing means The fixation position is detected from the calculation means, and the calculation means excludes the measurement value of the protein concentration according to the fixation disparity, corrects the position of the fundus infrared fluorescence image, or detects the fixation disparity. A partial image is corrected or complemented to form a single fundus image. Hereinafter, the present invention will be described in detail with reference to the accompanying drawings.

  FIG. 1 illustrates an embodiment in which the ophthalmologic apparatus is configured as an ophthalmologic measurement apparatus that measures the turbidity (hereinafter, exemplified as protein concentration) of the anterior eye portion to be examined.

  In FIG. 1, laser light emitted from a laser light source 11 passes through a mask 12 and a relay lens 13 and enters a scan mirror 14. Here, the scan mirror axis is different from that shown in the figure and is driven in parallel with the paper surface. The laser beam is reflected by the scan mirror 14 and vibrates up and down in the figure, and is imaged by the projection lens 16 on the measurement point 1b in the anterior eye portion (anterior chamber) 1a of the eye 1 to be examined.

  In the anterior chamber 1a of the eye to be examined, the scattered light of the laser light from albumin, globulin, etc. passes through the objective lens 21 and is reflected by the mirror 22, passes through the lens 23, the mask 24, and the filter 25, and passes through the photoelectric conversion element 26. Received light. In this case, the photoelectric conversion element 26 is a measuring unit that receives the side scattered light from the anterior segment 1a and measures the protein concentration in the anterior ocular aqueous humor. ) To be examined. In order for the photoelectric conversion element 26 to receive side scattered light from the anterior segment 1a, the measurement optical axis and the illumination optical axis are set at an angle of about 90 degrees.

  The signal from the photoelectric conversion element 26 is amplified by an amplifier 27, the turbidity of the anterior eye part, that is, the protein concentration is measured, the protein concentration value is calculated by the calculation unit (calculation means) 28, and the measurement result is monitored 29. Is displayed.

  An internal fixation target LED (light emitting diode) 30 is provided to fixate the eye to be examined, and the subject is fixing the target LED 30 during measurement. In addition, an anterior-eye illumination infrared LED (light-emitting diode) 31 is disposed so that the fixation state can be observed. The anterior eye portion 1a is illuminated by the infrared light of the infrared LED 31, and the image is connected to a moving image pickup means (hereinafter referred to as an infrared CCD) 33 constituted by an infrared CCD having sensitivity to the infrared light by the lens 32. Imaged. The infrared image from the infrared CCD 33 is stored in the memory 34, read out, and displayed on the monitor 37 via the switch 35. Further, the image in the memory 34 is image-processed by a position detection circuit (fixation position detection means) 35, and a fixation disparity is detected by detecting a light amount distribution in the anterior eye part, particularly in the vicinity of the pupil. The result is output to the calculation unit 28. The light receiving axis of the infrared CCD 33 is aligned with the fixation direction and is set to about 30 degrees in the direction of the measurement axis from the illumination axis.

  Further, in order to display the measurement range for the measurement point 1b and the depth d from the cornea to the examiner, an LED 40, a mask 41 with a measurement window and an index, and a lens 42 are arranged. Is received by the TV camera 44 via the mirror 22 and the lens 43 and displayed on the monitor 37 via the switch 36. When the index is matched with the front surface of the cornea (center of the pupil) in the normal eye, the measurement window is set to be positioned approximately in the middle between the cornea and the lens, and the examiner observes the image of the TV camera 44. Thus, alignment can be performed.

  In such a configuration, the examiner instructs the subject to fixate the internal fixation target LED 30, and at the same time performs alignment so that the index image of the mask 41 comes to substantially the center of the pupil. The alignment is performed by observing an image received by the TV camera 44 on the monitor 37. When the alignment is completed, the measurement point 1b is always at a substantially constant position, so the laser light source 11 is turned on and the anterior eye portion 1a is irradiated with the laser light. Side scattered light from the measurement point 1b of the anterior segment is received by the photoelectric conversion element 26, and the signal is input to the calculation unit 28, and the protein concentration value (flare value) is calculated by the calculation unit 28.

  At this time, the image of the anterior segment irradiated by the infrared LED 31 is received by the infrared CCD 33 and the image is sequentially stored in the memory 34 in association with the measurement time as a still image, which is stored in the position detection circuit 35. The image is read out and processed, and a fixation position or fixation disparity is continuously detected during the measurement period. This state is illustrated in FIG. 2, and the signals of the XX and YY lines passing through the index image 41a of the mask 41 are taken out, and the boundary edge of the pupil (or iris) is detected from the light quantity distribution. The position detection circuit 35 compares the distance from the index image 41a to the detected boundary edge in each of the XX line and the YY line, and whether the index image 41a is within the allowable range or not. It is determined whether or not it is located at approximately the center 2 of both boundaries of the pupil. If it is not within the allowable range, fixation disparity is detected (detection of such fixation disparity is also described in Patent Document 3).

  Instead of detecting the fixation disparity from the deviation of the index image 41a from the pupil center 2, the coordinates of the position of the pupil center 2 are obtained continuously during the measurement period as the fixation position, and this is determined in advance. The detection may be performed by detecting whether or not the reference coordinates (coordinate values when there is no fixation disparity). In this case, the image near the pupil is scanned with a plurality of scanning lines to extract the outline of the pupil, and the average value of the maximum and minimum values of the X coordinate of the outline is determined as the X coordinate value of the pupil center 2; A deviation from the reference coordinate value is measured using the average value of the maximum value and the minimum value of the Y coordinate as the Y coordinate value. Then, the arithmetic unit 28 detects a fixation disparity when the difference between the coordinate values exceeds a predetermined value.

  FIG. 3A shows the flare value calculated by the calculation unit 28, and shows the seventh measurement state (N = 7). The horizontal axis represents time, and the vertical axis represents the signal value (SIG) of the photoelectric conversion element 26. BG1 and BG2 are background values, and the average value is adopted as the background value. In this measurement, flare is calculated as 21.4. When “0.4”, an alignment failure occurs, and the position detection circuit 35 outputs position information indicating fixation disparity, and “F” indicating this is shown.

  FIG. 3B shows the measurement results of the eighth measurement from the first measurement (N = 1). If the measurement state is not good, a warning “WA” is attached and displayed. “S” indicates a poor S / N ratio, “F” indicates a poor alignment due to fixation disparity, “B” indicates a large difference in background values in time series, and “C” indicates that there are many cells. . In this case, “*” is added to those that are considered to be measurement errors, and the data is omitted and aggregated. The first “*” is a measurement error because of the large amount of background light, and “*” at the time of the eighth measurement is that the position detection circuit detects that the fixation disparity is large. However, in the seventh measurement, the fixation disparity “F” is detected. In this case, since the deviation is small, the data is collected without being omitted.

  As described above, the arithmetic unit 28 corrects the flare value (average value AV and standard deviation SD) based on the fixation information (fixation deviation) obtained from the position detection circuit 35. In this correction, when the calculation unit 28 determines that the fixation disparity exceeds a predetermined value and is large, the calculation unit 28 omits the flare values at that time and totals them, and calculates the average value AV and standard deviation of the flare values. This is done by calculating SD. If the fixation disparity period exceeds a predetermined time, an error display may be performed so as to invalidate the measurement itself.

  FIG. 4 shows a second embodiment of the present invention. In this embodiment, the ophthalmologic apparatus is configured as an infrared fluorescent fundus camera that captures an infrared fluorescent image of the fundus.

  In the ophthalmologic apparatus shown in FIG. 4, the apparatus main body 60 is provided with an illumination optical system that illuminates the fundus and an imaging optical system that forms an image of the illuminated fundus. In the illumination optical system, light emitted from a light source 61 such as a halogen lamp and light reflected by a concave mirror 62 pass through an infrared transmission visible light cut filter 63 and a strobe 64 that is a photographing light source, and an infrared fluorescent exciter filter. The light is incident on 65 and illuminates the ring slit 66 arranged at a position conjugate with the anterior eye portion (pupil) 1a of the eye 1 to be examined. The infrared illumination light from the ring slit 66 passes through the lens 67, the black spot plate 68 for removing the reflection of the objective lens 72, the half mirror 69, and the relay lens 70, and has total reflection with a hole having a hole in the center. After being reflected by the mirror 71, it passes through the objective lens 72, enters the fundus 1 c from the anterior segment 1 a of the eye 1 to be examined, and illuminates the fundus 1 c with infrared light.

  Reflected light from the fundus oculi 1c is received through the objective lens 72, passes through the hole of the perforated total reflection mirror 71, passes through the photographing aperture 81, the focus lens 82, and the imaging lens 83, and is reflected by the half mirror 84. The light is reflected and enters the half mirror 86 through a field stop 85 disposed at a position conjugate with the fundus 1c. The infrared light transmitted through the half mirror 86 is reflected by the mirror 88, passes through the imaging lens 87, and enters a moving image pickup means (hereinafter referred to as CCD) 90 constituted by an infrared CCD having sensitivity to infrared light. Then, the signal is input to the monitor 91, and the fundus moving image is displayed on the monitor 91.

  Further, the internal fixation lamp 93 is turned on, and the examiner can ensure alignment and focusing operations by having the subject gaze at the fixation lamp. For the focusing operation, the illumination optical system is provided with a focus dot light source 80, and a light beam from the light source 80 is incident on the fundus 1 c through the half mirror 69, and the focus dot light source 80 moves in accordance with the movement of the focus lens 72. Since the position changes, the examiner can focus on the eye to be examined by observing the focus dot on the monitor 91. Further, since the anterior segment lens 92 is inserted at the initial stage of alignment, the examiner can confirm the image of the anterior segment 1 a of the eye 1 to be examined on the monitor 91.

  The fundus image captured by the CCD 90 is sequentially stored as a still image in the memory 92 in association with the shooting time, and the image is processed by the position detection circuit (fixed position detection means) 110 as will be described later. Thus, the fixation position or fixation disparity of the eye to be examined is continuously detected during the imaging period.

  On the other hand, the infrared light reflected by the half mirror 86 passes through the infrared fluorescent barrier filter 90 via any one of at least two variable magnification lenses 97a and 97b, and has an infrared sensitivity. Light is received by an imaging means (hereinafter referred to as CCD) 103 constituted by a CCD or the like. The CCD 103 serves as an eye information acquisition unit that captures an infrared fluorescent image of the fundus and acquires eye information (infrared fluorescent image).

  The switch (photographing switch) 96 is a switch for photographing an infrared fluorescent image with the CCD 103. When a fluorescent agent is intravenously injected and a predetermined time has passed, the infrared ray that has passed through the infrared fluorescent exciter filter 65 is switched. Since an infrared fluorescent image is generated on the fundus by the excitation light, the switch 96 is operated. When the switch 96 is operated, the CCD 103 is activated by the operation signal, and capturing of a moving image of an infrared fluorescent image of the fundus is started. This infrared fluorescent image is displayed on the monitor 111 and stored in the memory 104. Further, the stored image is read out and input to the calculation means 112 configured by a CPU or the like, and is corrected based on fixation information obtained from the position detection circuit 110, and the corrected image is recorded in the recording device 113. To be recorded. The recorded image can be displayed on the monitor 114.

  In FIG. 4, a position conjugate with the fundus 1c of the eye 1 to be examined is indicated by R, and a position conjugate with the anterior eye part (particularly the pupil) is indicated by P.

  In such a configuration, since the infrared transmission visible light cut filter 63 and the infrared fluorescent exciter filter 65 are inserted in the illumination optical path, the fundus is illuminated with infrared light, and the fundus image is the objective lens 72 and the focus lens 82. The image is formed at the position of the field stop 85 by the imaging lens 83. Since the fundus image of the field stop 85 passes through the half mirror 86 and is re-imaged on the imaging surface of the CCD 90 by the imaging lens 87, the fundus image is displayed on the monitor 91 as a black and white moving image. A fundus image can be observed through the screen 91. The examiner can perform alignment and focusing operations by having the examinee gaze at the fixation lamp 93.

  Further, the fundus image of the CCD 90 is sequentially stored as a still image in the memory 92, and the image is input to the position detection circuit 110, and the fixation position is detected continuously during the photographing period. This is illustrated in FIG. In the position detection circuit 110, the image of the memory 92 is captured, and the position coordinates (xn, yn) of the central portion 3a are acquired as a fixation position by detecting the light amount distribution of the fundus feature point 3 (for example, the nipple). Is done. This position coordinate is obtained in the same manner as described in connection with FIG. That is, the fixation position is obtained by scanning the region near the nipple 3 to detect the contour line of the nipple 3 and calculating the average value of the maximum value and the minimum value of the X coordinate of the contour line as the X coordinate value of the central portion 3a. The average value of the maximum value and the minimum value of the Y coordinate can be obtained as the Y coordinate value. The position of the central portion 3a varies depending on the fixation state of the eye to be examined, and its position coordinates (x1, y1), (x2, y2),. . . . . (Xn, yn) is illustrated in FIGS. 5 (A), (B), and (C).

  When the alignment is completed, the fluorescent agent is intravenously injected, and an infrared fluorescent image is generated on the fundus. Therefore, the switch 96 is operated. As a result, a moving image of the fundus is captured by the CCD 103, and an infrared fluorescent image of the fundus is stored in the memory 104 and displayed on the monitor 111.

  The infrared fluorescent image of the fundus is taken by the CCD 103 for several tens of minutes after it appears. However, if the subject's fixation is insufficient during the imaging, the fundus moves with respect to the apparatus, so that the infrared fluorescent image is captured differently depending on the imaging time. Infrared fluorescent photographing generally tends to have a shortage of light, so there are cases where image processing such as a method of increasing the gain of the CCD or addition processing is performed. However, when the gain is increased, a clear image cannot be obtained due to noise, and in the case of image processing, noise is reduced, but if the fixation is shifted, the position of the fundus image is also shifted. When the image processing is performed, the images whose positions are shifted are added to each other, and as a result, a clear image cannot be obtained. Therefore, in the present invention, the calculation means 112 corrects the infrared fluorescent image photographed by the CCD 103 based on the fixation information obtained from the position detection circuit 110. This correction is illustrated in FIG.

  In FIG. 6, an infrared fluorescent image of the fundus is taken by the CCD 103 at times t1, t2, t3, and t4. The upper row is an image from the CCD 90 at each photographing time, the middle row is an image of the CCD 103, and the lower row is a corrected image of the CCD 103.

  At time t1, the fixation position coordinates (x1, y1) are acquired by the position detection circuit 110. Since this fixation position corresponds to a predetermined fixation position, the calculation unit 112 stores the CCD 103 stored in the memory 104. The infrared fluorescent image is sent to the recording device 113 without correction. Then, the image is recorded on the recording device as an image at time t1. At time t2, the fixation position is deviated, and its coordinates are deviated by Δx and Δy compared to time t1. The arithmetic means 112 corrects the image in the memory 104 when the deviation is within the allowable range and can be corrected. That is, an image shifted by Δx * m in the horizontal direction and Δy * m in the vertical direction is created as a corrected image and output to the recording device 113. Here, m is the ratio of the imaging magnification of the CCD 103 to the CCD 90.

  On the other hand, since the fixation disparity is large at time t3 and exceeds the allowable value, the image of the CCD 103 is deleted and is not recorded in the recording device 113. On the other hand, since the deviation is within the allowable range at time t4, correction is performed in the same manner as at time t2. In this case, the corrected image is replaced with the deleted image at time t3.

  In this way, even if there is a fixation disparity, a correction image similar to that obtained in a state without fixation disparity is obtained at the time, so when performing image processing such as addition of multiple images, There is no image shift and a clearer moving image can be obtained.

  Regarding the angle of view (imaging magnification) of the CCDs 90 and 103, since the CCD 90 is used for observation, the optical system is designed to have a wide angle (angle of view of 50 degrees). The variable magnification lenses 97a and 97b can be selected from two types (view angles of 50 degrees and 35 degrees). This is illustrated as an image B (view angle of 50 degrees) and an image A (view angle of 35 degrees) in the upper right of FIG. In the present embodiment, the image of the CCD 103 is also taken at a wide angle like the image of the CCD 90. However, since the angle of view of the obtained moving image is slightly smaller than 50 degrees in both the vertical direction and the right-right direction, it may be converted to an angle of view of 35 degrees generally used for infrared fluorescence. In FIG. 6, for the sake of explanation, the image of the CCD 90 is schematically shown as being taken at an angle of view of 50 degrees and the image of the CCD 103 is taken at an angle of view of 35 degrees.

  FIG. 7 shows a third embodiment of the present invention. In this embodiment, the ophthalmologic apparatus is configured as a spectral fundus camera that captures a spectral image of the fundus.

  In the ophthalmologic apparatus shown in FIG. 7, parts having the same or similar functions as those in FIG. 4 are denoted by the same reference numerals, and detailed description thereof is omitted.

  In the embodiment of FIG. 7, the half mirror 86 in the embodiment of FIG. 4 is replaced with an infrared transmission visible light reflection mirror 86 '.

  In addition, in order to perform spectroscopic analysis of the fundus image, a mirror 120 that is rotated using a mirror rotating device 121 configured by, for example, a stepping motor is disposed at the pupil conjugate position P, and the mirror rotating device is configured by a CPU or the like. Then, it is driven intermittently by the control / calculation means 115 that performs control and computation. The fundus image reflected by the mirror 120 passes through the lens 122, is reflected by the mirror 123, subsequently passes through the slit 124, is reflected by the mirror 125, passes through the lens 126, and enters the spectroscopic element 127. The spectroscopic element 127 has the same configuration as that of the prism / grating / prism (PGP) described in Japanese Patent Application Laid-Open No. 2002-224041, and the fundus image formed by the slit 124 is converted into a direction perpendicular to the longitudinal direction of the slit. The light is dispersed over a predetermined wavelength bandwidth. The spectroscopic fundus image passes through the lens 128 and enters an imaging means (hereinafter referred to as a CCD) 129 constituted by a CCD or the like. A spectroscopic image of the fundus slit image is taken, and the spectroscopic image is stored in the memory 130. Is done.

  In this way, the optical system to the CCD 90 is a fixed optical system, whereas the optical system to the CCD 129 is a scanning optical system, and an image obtained by the fixed optical system (CCD 90) is the fundus position ( The image signal obtained by the scanning type optical system (CCD 129) is used for obtaining a spectral image.

  With such a configuration, at the time of alignment, the infrared transmission visible light cut filter 63 is inserted in the optical path, and the image from the CCD 90 is observed on the monitor 91, whereby alignment and focusing operations are performed as in the second embodiment.

  When the alignment is completed, the switch 96 is operated, the infrared transmission visible light cut filter 63 is removed from the optical path, and the fundus is illuminated by the light source 61. The image of the fundus image by the infrared light component is transmitted through the infrared transmission visible light reflection mirror 86 ′, received by the CCD 90, displayed on the monitor 91, and sequentially stored as a still image in the memory 92, as shown in FIG. Similarly to the example, fixation position coordinates are continuously detected by the position detection circuit 110 (FIG. 5), and fixation information or fundus position information is acquired.

  On the other hand, the operation of the switch 96 causes the control / calculation means 115 to drive the stepping motor and rotate the mirror 120 step by step. The image of the fundus image by the visible light component is reflected by the infrared transmission visible light reflection mirror 86 ′ and enters the mirror 120. According to the rotation of the mirror, the line position of the fundus image formed on the slit 124 changes, and according to the position of the mirror 120, the slit image at each line position of the fundus is dispersed by the spectroscopic element 127 and separated. The captured image is taken by the CCD 129. Spectral data of the fundus slit image taken at each line position photographed by the CCD 129 is taken into the memory 130 in synchronization with the fundus line position obtained from the mirror rotating device 121 and stored for each line.

  This state is illustrated in FIGS. 8 and 9, and first, the position of the rotating mirror 120 is positioned so that a slit image at the vertical line position P <b> 1 at the left end of the fundus is photographed. Is formed with a fundus slit image at line P1. The spectroscopic element 127 converts the slit image into horizontal lines Q1, Q2,. . . . . Spectral decomposition is performed on wavelengths λ1 to λk with respect to Qm. Therefore, as shown in the upper right of FIG. 8, the CCD 129 images the spectral intensity of the wavelengths λ1 to λk for the slit images Q1 to Qm of the line P1 as a spectral image. This spectral image is stored in the memory 130 as spectral data on the line P1 at time t1 in synchronization with the signal from the rotary mirror drive mechanism 121. At this time, the position detection circuit 110 detects the fixation position based on the image from the CCD 90, and outputs the fixation position coordinates (x1, y1) at time t1 to the control / calculation means 115. The relationship between the slit image at this time t1 and the fixation position is shown at the top of FIG.

  Since the rotating mirror 120 is rotated by a predetermined amount, the spectral data of the fundus slit image at the lines P2 to Pn are sequentially photographed, and the spectral data of the slit image at each line is obtained at each position P2 to Pn ( It is stored in the memory 130 every time t2 to tn), that is, for each line. The spectral data of the slit images at the lines P2 to Pn are shown on the right side of FIG. FIG. 9 shows the relationship between the slit images and the fixation position coordinates (x2, y2) to (xn, yn) at the respective line positions P2 to Pn (time t2 to tn).

  Each line P1. . . . . Since the width of Pn is selected so that the image width at the slit 124 of the line is equal to the slit width of the slit 124, the rotating mirror 120 is rotated stepwise by an amount corresponding to the slit width, The entire area is scanned without a gap with a line width corresponding to the slit width.

  In this way, when a spectral image of the fundus slit image at each line position is captured, the control / calculation unit 115 reads the spectral image at each line position P1 to Pn from the memory 130, and each wavelength λh (h = 1 to k), the fundus image of only the wavelength λi is reconstructed by obtaining the values of (Pi, Qj) (i = 1 to n; k = 1 to m). This state is illustrated as a fundus image of each wavelength λ1 to λk at the bottom of FIG. Since each fundus image is reproduced as an image having a spectral intensity of a wavelength unique to the fundus image, it becomes an extremely effective information source for fundus diagnosis.

  The above example is an ideal case in which the fixation position detected by the position detection circuit 110 is substantially the reference position and no fixation disparity occurs, but the entire fundus is scanned with a slit, and the entire spectrum is measured. Since the measurement time for measuring the characteristic is about several tens of seconds, it is longer than the fixation maintenance time of the eye to be inspected, and usually fixation disparity occurs. For example, when fixation disparity occurs in the line direction at the time of the line Pj, when the fundus image at each wavelength is reconstructed, the fundus image after the line Pj is displayed before that as shown in FIG. If the blinking or fixation disparity becomes large at the line Pk, the spectral image acquisition at that line fails, and the image at that portion is lost.

  Therefore, in the present invention, as shown in the lower part of FIG. 8, when the control / calculation unit 115 reproduces the fundus image at each wavelength based on the spectral image at each line P1 to Pn, each line Pi (i = The slit-like fundus image reproduced in 1 to n) is acquired as a partial image and stored in a memory for each wavelength. Then, when the fixation disparity is detected, the control / calculation unit 115 corrects the partial images at that time and combines the partial images to form one fundus image. In addition, spectroscopic measurement is performed a plurality of times in order to correct a defective partial image by complementation. Therefore, in the third embodiment, the control / calculation unit 115 is a unit that scans the fundus and acquires a slit-shaped partial image (information on the eye to be examined). Hereinafter, a method for correcting (complementing) this partial image to form a fundus image similar to the case where there is no fixation disparity will be described.

  As described with reference to FIG. 8, the control / calculation unit 115 reproduces (reconstructs) a fundus image of each wavelength λi (i = 1 to k) from the spectral image. FIG. 12A shows a fundus image having a wavelength λi. In this case, the fundus image is a partial image Ai (i = 1 to n) reproduced from the spectral image of the line Pi (i = 1 to n). Are adjacent to each other with no gap, and the upper and lower sides are matched to form a single composite image. Therefore, an image memory for each wavelength is provided in the control / calculation means 115 to store the reproduced partial image.

  FIG. 12B shows an image memory having a wavelength λi provided in the control / calculation means 115. Here, the wavelength λi is representative, but the wavelengths λ1, λ2,. . . . . The memory for λn has the same configuration. Now, when the first measurement is performed, a spectral image of each line Pi (i = 1 to n) is obtained with the rotation of the mirror 120, so that the control / calculation means 115 has the wavelength λi from each spectral image. Extracting the partial images A1,. . . . . An can be reproduced.

  This corresponds to the slit-shaped partial images A1,. . . . . An, which is shown as P1, P2,. . . . . This corresponds to data obtained by extracting data of the wavelength λi portion of the spectral image on the Pn line over Q1 to Qm. Since each partial image Ai (i = 1 to n) is an image at time ti (i = 1 to n), as shown in FIG. An image Ai is stored. Further, as described with reference to FIG. 9, the fixation position coordinates (xi, yi) at each time ti are acquired by the position detection circuit 110, so that they are also stored in association with the time ti. To do. In FIG. 12B, (1) is added to indicate that each data is the first measurement.

  Here, there is no fixation disparity over the entire measurement time, and the control / calculation unit 115 compares the fixation position coordinates (xi, yi) at each time ti with a reference value, and the fixation disparity is smaller than a predetermined deviation. When the determination is made, the measurement is completed, and the control / calculation unit 115 synthesizes the partial images Ai into one fundus image. This corresponds to the fundus image shown in the lower part of FIG. 8 and in FIG.

  On the other hand, as shown in FIG. 10 (B), fixation disparity or image loss occurs in the lines Pj and Pk, and the control / calculation unit 115 has a large fixation disparity at times tj and tk. If it is determined that it is out of the permissible range, or if it is determined that the partial image cannot be reproduced in the first place, a signal that prompts the examiner to remeasure is generated.

  In such a case, re-measurement is performed, and the same operation and processing as the first time are performed. How many times the measurement is performed is related to the quality of the previous measurement or the previous measurement. For example, if the time when the fixation disparity that is unacceptable in the first measurement occurs is small, the measurement can be performed 2-3 times. If a considerable fixation disparity is detected, the number of measurements is increased accordingly.

  Here, FIG. 11 shows an example in the case where N times (N> 1 integer) measurement is performed, and the data stored in the memory is shown in FIG. It is shown with (N) attached.

  In the example shown in FIG. 10 (A), fixation disparity is observed after the line Pj, and missing images are detected at the line Pk. Therefore, the re-measurement is performed and the partial image up to the first line Pj is obtained. By synthesizing the partial images after the line Pj with no fixation disparity due to re-measurement, it is possible to reproduce a fundus image with no deviation and no image omission.

  In the case shown in FIG. 10A, the fixation disparity after the line Pj is the fixation disparity in the line direction, so that the partial images after the line Pj are not measured again. You may make it move by the deviation | shift and synthesize | combine with the partial image before Pj. However, since there is a missing image at the line Pk, remeasurement is performed to complement the image of that portion. If the partial image of the line Pk can be acquired by remeasurement, the missing image is complemented with the partial image. The fundus image obtained in this manner is shown in FIG. 10B, and a fundus image in which there is no shift at the XX line and the Pk image is complemented is obtained. In such a case, since the partial images after the line Pj are reproduced with being shifted in the line direction, the portions indicated by hatching in the periphery are cut, and the entire image area is reduced. It is reproduced.

  In addition, a plurality of spectral measurements are performed at least twice, and each partial image Ak (k = 1 to n) is extracted as a partial image with the smallest fixation disparity from each time data, and the entire fundus image is synthesized. You may make it do. As a result, a single fundus image is formed from partial images with little fixation disparity, and a good fundus image can be obtained.

  In Example 3, observation is performed with infrared light and imaging is performed with visible light. However, depending on the state of the eye to be examined, observation may be performed with visible light using a mydriatic agent. In addition, the wavelength of light at the time of photographing need not be limited to visible light, and may be appropriately selected within a range including infrared light according to a region where a spectral image is to be obtained. What is necessary is just to insert filter 65 '(it shows with the dashed-dotted line in FIG. 7) in the optical path suitably as needed. Further, it is necessary to change the wavelength characteristics of transmission and reflection of the mirror 86 ′ in accordance with the selection. Therefore, it is convenient to have a structure that can be easily replaced with a filter or mirror 86 ″ having different wavelength characteristics.

(Example 1) which is the optical diagram which showed the optical structure of the ophthalmologic apparatus in the case of implementing as an apparatus which measures the protein concentration of the anterior ocular segment. FIG. 3 is an explanatory diagram illustrating a method for detecting a fixation position in the first embodiment. It is the table | surface which showed the calculation result of protein concentration. (Example 2) which is the optical diagram which showed the optical structure of the ophthalmologic apparatus in the case of implementing as an apparatus which performs infrared fluorescence imaging | photography. 10 is an explanatory diagram illustrating a method for detecting a fixation position in Embodiment 2. FIG. It is explanatory drawing which showed the flow which correct | amends an infrared fluorescence image. (Example 3) which is the optical diagram which showed the optical structure of the ophthalmologic apparatus in the case of implementing as an apparatus which acquires the spectral image of a fundus. It is explanatory drawing which showed the flow which acquires a spectral image and reconstructs a fundus image. It is explanatory drawing which showed the response | compatibility with the slit image of a fundus, and a fixation position at each photographing time. (A) is an image figure of the fundus when there is a fixation disparity, and (B) is an image figure of the fundus obtained by correcting the image of the fixation disparity part. It is explanatory drawing which showed the response | compatibility of the slit image at the time of the Nth measurement, and a fixation position at each imaging time. (A) is the image figure which showed the partial image reproduced from a spectral image, (B) is explanatory drawing which showed the content of the memory which stores a partial image and fixation information.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Eye to be examined 26 Photoelectric conversion element 28 Calculation part 33 Infrared CCD
35 Position detection circuit 90, 103 CCD
DESCRIPTION OF SYMBOLS 110 Position detection circuit 112 Calculation means 115 Control / calculation means 124 Slit 127 Spectroscopic element

Claims (9)

Eye information acquisition means for acquiring eye information;
Fixation position detection means for continuously detecting the fixation position of the eye to be examined;
Arithmetic means for correcting eye information based on fixation information obtained by continuously detecting fixation positions;
In an ophthalmic device having
The subject eye information acquisition means is means for acquiring continuous partial image data by scanning the fundus,
When the fixation disparity is detected, the arithmetic means corrects the partial image data obtained at that time and synthesizes the partial image data to form one fundus examination eye image .   The subject eye information acquisition means is a measurement means for measuring anterior eye turbidity, and the calculation means excludes a measurement value of the turbidity at the time when fixation disparity is detected during turbidity measurement. The ophthalmologic apparatus according to claim 1, wherein the operation is performed in the same manner.   3. The ophthalmologic apparatus according to claim 1, wherein the fixation position detection unit detects a fixation position from a light amount distribution of an anterior segment image captured by a moving image capturing unit of the anterior segment.   The eye information acquisition unit is an imaging unit that captures an infrared fluorescence image of the fundus, and the calculation unit corrects the position of the fundus infrared fluorescence image captured according to fixation disparity. The ophthalmic apparatus according to claim 1.   5. The ophthalmologic apparatus according to claim 1, wherein the fixation position detection unit detects a fixation position from a light amount distribution of a fundus image captured by a fundus moving image imaging unit.   The eye information acquisition unit is a unit that scans the fundus to acquire a continuous slit-shaped partial image, and the calculation unit corrects the partial image obtained when a fixation disparity is detected. The ophthalmologic apparatus according to claim 1, wherein the partial images are combined to form a single fundus image.   The ophthalmic apparatus according to claim 6, wherein the partial image is acquired a plurality of times, and the correction of the partial image is performed by complementing the corresponding partial image performed at another time.   The ophthalmologic apparatus according to claim 6 or 7, wherein the fixation position detection unit detects a fixation position from a light amount distribution of a fundus image captured by a fundus moving image imaging unit.   The ophthalmologic apparatus according to claim 6, wherein the partial image is a partial image including only a predetermined wavelength reproduced from a spectral image of the fundus.

Images