Abstract:
A multifunction ophthalmic apparatus, capable of examining different eye characteristics of an examinee&#39;s eye by a single apparatus, has a first examination part including a first examination optical system for examining a first eye characteristic, a second examination part including a second examination optical system for examining a second eye characteristic, a first image-pickup element which picks up a first image of an anterior-segment of the eye in first examination, a second image-pickup element which picks up a second image of the anterior-segment in second examination, a display unit which displays the images, an input unit which inputs adjustment information on at least one of respective brightness and respective contrast of the images, and a control unit which controls to switch displays between the images in accordance with switching between the examinations to adjust at least one of the brightness and contrast of the displayed image based on the information.

Description:
BACKGROUND OF THE INVENTION  
       [0001]     1. Field of the Invention  
         [0002]     The present invention relates to an ophthalmic apparatus for examining (including measuring, photographing and the like) different eye characteristics of an eye of an examinee.  
         [0003]     2. Description of Related Art  
         [0004]     Conventionally, a multifunction ophthalmic apparatus capable of examining different eye characteristics of an eye of an examinee by a single apparatus is proposed. In this kind of apparatus, an observation optical system having an image-pickup element for picking up an image of an anterior-segment of the eye and a display unit including a monitor for displaying the picked-up image are arranged, so that, at the time of examinations of the respective eye characteristics, alignment of the apparatus with respect to the eye and the like are performed while the image of the anterior-segment is observed.  
         [0005]     In the examinations of the respective eye characteristics, there is a case where constitutions of the observation optical system and an alignment optical system used therefor are different. In such a case, brightness and contrast of the images of the anterior-segment displayed on the monitor may be different in the respective examinations, and it takes a lot of trouble to adjust them every time the examination is performed.  
       SUMMARY OF THE INVENTION  
       [0006]     An object of the invention is to overcome the problems described above and to provide an ophthalmic apparatus capable of observing images of an eye of an examinee (images of an anterior-segment of the eye) suitable for respective examinations of different eye characteristics.  
         [0007]     To achieve the objects and in accordance with the purpose of the present invention, an ophthalmic apparatus has a first examination part including a first examination optical system for examining a first eye characteristic of an eye of an examinee, a second examination part including a second examination optical system for examining a second eye characteristic of the eye different from the first eye characteristic, a first image-pickup element which picks up a first image of an anterior-segment of the eye at the time of first examination by the first examination part, a second image-pickup element which picks up a second image of the anterior-segment at the time of second examination by the second examination part, a display unit which displays the first image and the second image, an input unit which inputs adjustment information on at least one of respective brightness and respective contrast of the first image and the second image, and a control unit which controls to switch displays between the first image and the second image in accordance with switching between the first examination and the second examination so as to adjust at least one of the brightness and the contrast of the displayed image based on the inputted adjustment information.  
         [0008]     Additional objects and advantages of the invention are set forth in the description which follows, are obvious from the description, or may be learned by practicing the invention. The objects and advantages of the invention may be realized and attained by the ophthalmic apparatus in the claims. 
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0009]     The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments of the present invention and, together with the description, serve to explain the objects, advantages and principles of the invention. In the drawings,  
         [0010]      FIG. 1  is a view showing a schematic configuration of an ophthalmic apparatus consistent with the present invention;  
         [0011]      FIGS. 2A and 2B  are views showing a schematic configuration of an inside of a main body when viewed from the side;  
         [0012]      FIG. 3  is a view showing a schematic configuration of optical systems arranged inside the main body and an air blowing mechanism in an intraocular pressure measurement part;  
         [0013]      FIG. 4  is a view showing a schematic block diagram of a control system of the present apparatus;  
         [0014]      FIG. 5  is a view showing an example of an environment setting screen in an eye refractive power measurement mode and a corneal shape measurement mode; and  
         [0015]      FIG. 6  is a view showing a schematic configuration of a partially modified embodiment of the optical systems arranged inside the main body. 
     
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS  
       [0016]     A detailed description of one preferred embodiment of an ophthalmic apparatus embodied by the present invention is provided below with reference to the accompanying drawings. In this embodiment, a multifunction apparatus which measures intraocular pressure, eye refractive power and a corneal shape will be taken as an example.  FIG. 1  is a view showing a schematic configuration of an ophthalmic apparatus consistent with the present invention.  
         [0017]     A mobile base  2 , on which a main body  1  is provided, is arranged on a base  3  movably in a right/left direction (referred to as an X-direction hereinafter) and a back/forth direction (a working distance direction, referred to as a Z-direction hereinafter). This movement is mechanically (or may be electrically) performed through operation of a joystick  4 . Additionally, the main body  1  is arranged on the mobile base  2  movably in the X-direction, Z-direction, and an up/down direction (referred to as a Y-direction hereinafter). The movement in each of the directions is electrically performed based on a detection result on an alignment state of the main body  1  with an eye of an examinee. Further, the movement in the Y-direction is electrically performed also through operation of a rotation knob  4   a  of the joystick  4 .  
         [0018]     On the base  3 , a face-supporting unit  6  for supporting a face (a head) of the examinee is fixedly provided. Further, a forehead rest  7 , against which a forehead of the examinee is slightly pressed to be fixed, is provided to the face-supporting unit  6 . A measurement starting switch  5  is provided at the top of the joystick  4 . Projection windows  8   a  allow the passage of light from light sources  20  for anterior-segment illumination described later. Projection windows  8   b  allow the passage of light from light sources  80  for corneal shape measurement and alignment in the Z-direction described later. Projection windows  5   c  allow the passage of light from light sources  85  for the alignment in the Z-direction described later.  
         [0019]      FIGS. 2A and 2B  are views showing a schematic configuration of an inside of the main body  1  when viewed from the side (i.e., from a direction of the arrow A shown in  FIG. 1 ). Inside the main body  1 , an intraocular pressure measurement part  1   a  for performing noncontact measurement of the intraocular pressure of an eye E of the examinee is arranged movably in the Z-direction, and an eye refractive power/corneal shape measurement part  1   b  for measuring the eye refractive power and the corneal shape of the eye E is fixedly arranged above the measurement part  1   a . Further, a reflection mirror  9 , a reflection mirror  10 , a mirror moving unit  90 , and a moving unit  100  for the measurement part  1   a  are arranged.  
         [0020]     The measurement part  1   a  is moved in parallel in the Z-direction by the moving unit  100 . The moving unit  90  performs insertion and removal of the mirror  9  between the eye E and a nozzle  13  provided to the measurement part  1   a  in synchronization with the movement of the measurement part  1   a  in the Z-direction. In other words, when the measurement part  1   a  is moved from a retreat position in  FIG. 2A  to a measurement reference position in  FIG. 2B , the mirror  9  is moved from a state where the mirror  9  is inserted in front of the nozzle  13  (i.e., between the eye E and the nozzle  13 ) to a state where the mirror  9  is removed therefrom. In contrast, when the measurement part  1   a  is moved from the measurement reference position in  FIG. 2B  to the retreat position in  FIG. 2A , the mirror  9  is also moved from the removed state to the inserted state.  
         [0021]      FIG. 3  is a view showing a schematic configuration of optical systems arranged inside the main body  1  and an air blowing mechanism in the measurement part  1   a.    
         [0022]     Firstly, an air (fluid) blowing mechanism  102  in the measurement part  1   a  will be described. A cylinder  11  is for air compression. A piston  12  is moved inside the cylinder  11  by driving force of a rotary solenoid  113  described later. The air compressed inside the cylinder  11  by the movement of the piston  12  is blown from the nozzle  13  to a cornea Ec of the eye E. Two transparent glass plates  14  hold the nozzle  13 . A transparent glass plate  15  is provided behind the nozzle  13 . Behind the glass plate  15 , optical systems for observation and alignment described later are arranged. A pressure sensor  16  detects pressure inside the cylinder  11 .  
         [0023]     Next, the optical systems in the measurement part  1   a  will be described. In this regard, when using the measurement part  1   a  (i.e., at the time of intraocular pressure measurement), the mirror  9  is moved by the moving units  90  and  100  to the retreat position (removed state) where it does not influence the intraocular pressure measurement.  
         [0024]     Four infrared light sources  20  for anterior-segment illumination are arranged having an optical axis L 1  coincident with an axial line of the nozzle  13  as their center. An image of an anterior-segment of the eye E formed by the light sources  20  is transmitted through the glass plate  15 , a half mirror  21 , an objective lens  22 , a dichroic mirror  23 , and a filter  24 , each arranged on the optical axis L 1 , to be picked up by a CCD camera  25  being an image-pickup element (these components constitute an observation optical system). Besides, the dichroic mirror  23  has a property of transmitting infrared light and reflecting visible light. Additionally, the filter  24  has a property of transmitting light from the light sources  20  and a light source  30  described later, and not transmitting light from a light source  40  described later. The image of the anterior-segment of the eye E picked up by the camera  25  is displayed on a monitor  26  described later. Besides, the light sources  20  are configured so that light intensity thereof is adjustable.  
         [0025]     The infrared light source  30  is for alignment in the X- and Y-directions, and the light therefrom is transmitted through a projection lens  31 , the half mirror  21 , and the glass plate  15 , to be projected onto the cornea Ec from the front (these components constitute an alignment target projection optical system). An image of corneal reflection by the light source  30  (corneal reflex of the light source  30 ) is transmitted through the glass plate  15  to the filter  24  to be picked up by the camera  25  (these components constitute an alignment target detection optical system), and is utilized in the alignment in the X- and Y-directions. Besides, images of corneal reflection by the light sources  20  (corneal reflexes of the light sources  20 ) may also be utilized in the alignment in the X- and Y-directions (for details, see U.S. Pat. No. 6,022,108 corresponding to Japanese Patent Application Unexamined Publication No. Hei10-71122). A visible light source  35  is for fixation target projection, and light from a fixation target  36  illuminated by the light source  35  is transmitted through a projection lens  37 , the dichroic mirror  23 , the objective lens  22 , the half mirror  21 , and the glass plate  15 , to head for the eye E.  
         [0026]     The infrared light source  40  is for detection of a deformation state of the cornea Ec, and the light therefrom is made into an approximately parallel light bundle by a collimator lens  41  to be projected onto the cornea Ec. An image of corneal reflection by the light source  40  (corneal reflex of the light source  40 ) is transmitted through a photo-receiving lens  42 , a filter  43 , a half mirror  44 , and a pinhole plate  45 , to be photo-received on a photo-detector  46 . The filter  43  has a property of transmitting the light from the light source  40  and not transmitting the light from the light sources  20  and  30 . A corneal-deformation-state detection optical system (an intraocular pressure measurement optical system) constituted of these components is arranged such that a photo-receiving amount of the photo-detector  46  is at the maximum when the cornea Ec is in a predetermined deformation state (a flat state).  
         [0027]     In addition, the light source  40  and the collimator lens  41  are also utilized in alignment in the Z-direction (these components constitute an alignment target projection optical system), and the image of corneal reflection by the light source  40  is transmitted through the photo-receiving lens  42  to the half mirror  44  and enters a one-dimensional position detector  47  such as a PSD or a line sensor (these components constitute an alignment target detection optical system). When the eye E (cornea Ec) is moved in the Z-direction, an entering position of the image of corneal reflection by the light source  40  is also moved on the position detector  47 . Therefore, an alignment state in the Z-direction with respect to the eye E may be detected based on an output signal from the position detector  47 .  
         [0028]     Incidentally, for the sake of illustration,  FIG. 3  shows such that the optical system for detection of a deformation state of a cornea and the optical system for detection of the alignment state in the Z-direction are vertically arranged; however, they are primarily arranged horizontally with respect to the eye of the examinee.  
         [0029]     Next, optical systems in the measurement part  1   b  will be described. When the measurement part  1   b  is used (i.e., at the time of eye refractive power measurement and corneal shape measurement), the mirror  9  is moved by the moving units  90  and  100  to the measurement reference position (inserted state) in front of the nozzle  13 .  
         [0030]     The image of the anterior-segment of the eye E formed by the light sources  20  is reflected by the mirror  9 , and is transmitted through the mirror  10 , a half mirror  51 , a half mirror  52 , and an image forming lens  53 , each arranged on a measurement optical axis L 2  made coaxial with the optical axis L 1  by the mirror  9 , to be picked up by a CCD camera  54  being an image-pickup element (these components constitute an observation optical system). The image of the anterior-segment of the eye E picked up by the camera  54  is displayed on the monitor  26  described later.  
         [0031]     An infrared light source  60  is for the alignment in the X- and Y-directions, and light therefrom is transmitted through a projection lens  61 , a dichroic mirror  62 , the half mirror  52 , the half mirror  51 , the mirror  10  and the mirror  9 , to be projected onto the cornea Ec from the front (these components constitute an alignment target projection optical system). Incidentally, the dichroic mirror  62  has a property of transmitting visible light and reflecting infrared light. An image of corneal reflection by the light source  60  (corneal reflex of the light source  60 ) is transmitted through the mirror  9  to the image forming lens  53  to be picked up by the camera  54  (these components constitute an alignment target detection optical system), and is utilized in the alignment in the X- and Y-directions. Besides, the images of corneal reflection by the light sources  20  may also be utilized in the alignment in the X- and Y-directions. A visible light source  65  is for fixation target projection, and light from a fixation target  66  illuminated by the light source  65  is transmitted through a projection lens  67 , the dichroic mirror  62 , the half mirror  52 , the half mirror  51 , the mirror  10  and the mirror  9  to head for the eye E. In addition, the projection lens  67  is moved in the direction of an optical axis, so that the eye E is fogged.  
         [0032]     An infrared light source  70  is for eye refractive power measurement, and light therefrom passes through slits provided in a rotation sector  71 , and is transmitted through a projection lens  72 , a diaphragm  73 , a half mirror  74 , the half mirror  51 , the mirror  10 , and the mirror  9 , to be projected onto a fundus of the eye E while being scanned. The light reflected from the fundus is transmitted through the mirror  9 , the mirror  10 , the half mirror  51 , the half mirror  74 , a photo-receiving lens  75  and a diaphragm  76 , and is photo-received on a photo-receiving part  77  provided with a plurality of pairs of photodetectors. Incidentally, in connection with the optical system for the eye refractive power measurement, see U.S. Pat. No. 5,907,388 corresponding to Japanese Patent Application unexamined Publication No. Hei10-108836 for details.  
         [0033]     Four infrared light sources  80  for the corneal shape measurement and the alignment in the Z-direction are arranged having the optical axis L 1  as their center. Two of them are arranged in a horizontal direction of the apparatus, and the other two are arranged in a vertical direction of the apparatus, in order that each of their projection optical axes intersects at a predetermined angle with the optical axis L 1 . Light from the light sources  80  is transmitted through spot diaphragms  81  and collimating lenses  82  to be projected onto the cornea Ec (these components constitute an alignment target projection optical system). Images of corneal reflection by the light sources  80  (corneal reflexes of the light sources  80 ) are transmitted through the mirror  9 , the mirror  10 , the half mirror  51 , the half mirror  52 , and the image forming lens  53 , to be picked up by the camera  54  (these components constitute an alignment target detection optical system). Besides, for details of the optical system for the corneal shape measurement, see Japanese Patent Application Unexamined Publication No. Sho61-85920.  
         [0034]     Two infrared light sources  85  for the alignment in the Z-direction are arranged having the optical axis L 1  as their center. Further, the light sources  85  are arranged in the horizontal direction of the apparatus so that each of their projection optical axes intersects at a predetermined angle with the optical axis L 1 . Light from the light sources  85  is transmitted through spot diaphragms  86  to be projected onto the cornea Ec (these components constitute an alignment target projection optical system). Images of corneal reflection by the light sources  85  (corneal reflexes of the light sources  85 ) are transmitted through the mirror  9 , the mirror  10 , the half mirror  51 , the half mirror  52 , and the image forming lens  53 , to be picked up by the camera  54 .  
         [0035]     Since the light from the light sources  80  is made into a parallel light bundle by the lenses  82 , even if a working distance (distance in the Z-direction) of the main body  1  with respect to the eye E is changed, a position of the image of corneal reflection is changed little. In contrast, since the light from the light sources  85  is a divergent light bundle, if the working distance is changed, a position of the image of corneal reflection is changed. Thus, an alignment state in the Z-direction may be detected from the positions of these images of corneal reflection (for details, see U.S. Pat. No. 5,463,430 corresponding to Japanese Patent Application Unexamined Publication No. Hei6-46999).  
         [0036]      FIG. 4  is a view showing a schematic block diagram of a control system of the present apparatus. Inputted into an image control part  140  are image signals from the camera  25  and the camera  54 . The image control part  140  has functions such as controlling to process the image signals to detect the images of corneal reflection by the respective light sources, to stitch the image signals to be outputted on the monitor  26  (display images on the monitor  26 ), and to superimpose letters, marks and the like on the image of the anterior-segment of the eye E. A display setting part  27  is for inputting adjustment information on brightness and contrast of the display screen (the display image) on the monitor  26 , and the adjustment information is inputted into a system control part  110 . The display setting part  27  is provided with a MENU button  27   a , an ENTER button  27   b , an up (↑) button  27   c , and a down (↓) button  27   d  (see  FIG. 5 ). A monitor control part  28  controls to adjust and set the brightness and the contrast of the monitor  26  based on an instruction signal from the system control part  110 . For the monitor control part  28 , an adjustment function provided to the monitor  26  may also be utilized.  
         [0037]     The image control part  140  is connected with the monitor control part  28  which is connected to the system control part  110 . In addition, the system control part  110  is connected with the likes of the display setting part  27 , a memory  141  for storing an adjustment value of the monitor  26  in digital form, a moving part  130  for moving the main body  1  three-dimensionally in the X-, Y- and Z-directions, the moving unit  90 , the moving unit  100 , the rotary solenoid  113  for moving the piston  12 , the photo-detector  46 , the position detector  47 , the photo-receiving part  77 , a memory  120  for storing measurement data, measurement conditions and the like, and a switch part  121  having a measurement-mode selecting switch, alight-intensity adjustment switch for adjusting the light intensity of the light sources  20  and the like.  
         [0038]     In the ophthalmic apparatus having the aforementioned constitution, its operations will be described. The present apparatus includes a first mode; the apparatus operates only in an eye refractive power measurement mode, a second mode; the apparatus operates only in a corneal shape measurement mode, a third mode; the apparatus operates only in an intraocular pressure measurement mode, a forth mode; the apparatus operates successively in the eye refractive power measurement mode and the corneal shape measurement mode, and a fifth mode; the apparatus operates successively in the eye refractive power measurement mode, the corneal shape measurement mode and the intraocular pressure measurement mode. These modes may be selected by the mode selecting switch in the switch part  121 . In the fifth mode, the apparatus firstly operates in the eye refractive power measurement mode and the corneal shape measurement mode, and then, it operates in the intraocular pressure measurement mode upon automatic switching to the intraocular pressure measurement mode. This is because, if the intraocular pressure is measured first, an influence of the blow of the compressed air and the like possibly remains. Hereinafter, the fifth mode will be described.  
         [0039]     In the eye refractive power measurement mode and the corneal shape measurement mode, the mirror  9  is inserted in front of the nozzle  13  and the image of the anterior-segment of the eye E is picked up by the camera  54 . The examiner performs rough alignment in the respective X-, Y- and Z-directions of the main body  1  with the eye E through operation of the joystick  4  and the rotation knob  4   a  while observing the image of the anterior-segment displayed on the monitor  26 .  
         [0040]     When each of the images of corneal reflection by the light sources  60 ,  80  and  85  is in a condition to be picked up by the camera  54 , the images are detected to be processed by the image control part  140 . The system control part  110  drives and controls the moving part  130  based on detection results on the images, and performs detailed (fine) alignment in the X-, Y- and Z-directions of the main body  1  with the eye E.  
         [0041]     Once the alignment state in each of the X-, Y- and Z-directions with the eye E falls respectively within a predetermined permissible range, the system control part  110  automatically controls to emit a trigger signal (or the examiner depresses the switch  5  to input the trigger signal in accordance with a display of alignment completion displayed on the monitor  26 ), and the eye refractive power is obtained based on phase differences of output signals from the respective photodetectors in the photo-receiving part  77 . In addition, the system control part  110  controls to obtain a position of the image of corneal reflection by the light sources  80  and calculate the corneal shape, based on an output signal from the camera  54 .  
         [0042]     In the fifth mode, when the eye refractive power measurement and the corneal shape measurement satisfy a predetermined condition for measurement termination such that the predetermined number of measurement results are obtained respectively, the system control part  110  automatically controls to emit a switching signal to the intraocular pressure measurement mode, and the eye refractive power measurement mode and the corneal shape measurement mode are switched to the intraocular pressure measurement mode. Based on the switching signal to the intraocular pressure measurement mode, the system control part  110  controls to turn off the light sources  60 ,  80 ,  85  and the like for the alignment in the eye refractive power measurement and the corneal shape measurement, and turn on the light sources  30 ,  40  and the like for the alignment of the intraocular pressure measurement. At the same time, the system control part  110  controls to move the measurement part  1   a  forward (in a direction toward the eye E), and thrust a tip of the nozzle  13  from a front surface of the main body  1 . At this time, the mirror  9  is removed from the front of the nozzle  13  in conjunction with the movement of the measurement part  1   a , and thereby it becomes possible to pick up the image of the anterior-segment of the eye E by the camera  25 , and each of the images of corneal reflection by the light sources  30  and  40  is brought in a detectable state. Further, the system control part  110  controls to switch the images displayed on the monitor  26  from the one picked up by the camera  54  to the one picked up by the camera  25  based on the switching signal to the intraocular pressure measurement mode. The examiner, if necessary, manually performs rough alignment and the like while observing the image of the anterior-segment displayed on the monitor  26 .  
         [0043]     When the image of corneal reflection by the light source  40  is in a state of entering the position detector  47 , the system control part  110  drives and controls the moving part  130  (or the moving unit  100 , or both of the moving part  130  and the moving unit  100 ) based on a detection result on the image, and performs detailed (fine) alignment in the Z-direction. Further, the moving part  130  is driven and controlled based on a detection result on the image of corneal reflection by the light source  30 , which is picked up by the camera  25 , to perform detailed (fine) alignment in the X- and Y-directions.  
         [0044]     Once an alignment state in each of the X-, Y- and Z-directions of the measurement part  1   a  with respect to the eye E falls respectively within a predetermined permissible range, the system control part  110  automatically controls to emit the trigger signal (or the examiner depresses the switch  5  to input the trigger signal in accordance with the display of alignment completion displayed on the monitor  26 ), and to drive the rotary solenoid  113 . When the piston  12  is moved by the driving of the rotary solenoid  113 , the air inside the cylinder  11  is compressed and blown from the nozzle  13  to the cornea Ec. The cornea Ec is gradually deformed by the blow of the compressed air, and when it reaches the flat state, the maximum amount of light enters the photo-detector  46 . The system control part  110  controls to calculate the intraocular pressure based on an output signal from the pressure sensor  16  and an output signal from the photo-detector  46 .  
         [0045]     Next, described will be a method for adjusting the brightness and the contrast of the image of the anterior-segment displayed on the monitor  26 , when those at the time of the eye refractive power measurement and the corneal shape measurement differ from those at the time of the intraocular pressure measurement.  
         [0046]     By depressing the button  27   a  on the display setting part  27 , an environment setting screen is displayed on the monitor  26 .  FIG. 5  is a view showing an example of the environment setting screen in the eye refractive power measurement mode and the corneal shape measurement mode, where an image F of the anterior-segment picked up by the camera  54  is displayed on the monitor  26 . At the left side of the lower part of the screen, displayed are an “RK” display  201  indicating the eye refractive power measurement mode and the corneal shape measurement mode, and a display  202  of an adjustment level of the brightness and a display  203  of an adjustment level of the contrast in these modes. At the right side of the lower part of the screen, displayed are an “NT” display  205  indicating the intraocular pressure measurement mode, and a display  206  of an adjustment level of the brightness and a display  207  of an adjustment level of the contrast in this mode. The adjustment level of each parameter of the brightness and the contrast is adjustable, for example, in 10 levels from 1 to 10. A cursor  200  indicates a selected item among the parameters.  
         [0047]     Here, in a case where the brightness and the contrast on the monitor  26  in the eye refractive power measurement mode and the corneal shape measurement mode are adjusted, the button  27   c  or the button  27   d  is depressed to move the cursor  200  to the parameter to be adjusted, and the button  27   b  is depressed to select the parameter, so that the adjustment level thereof becomes changeable. Then, by depressing the button  27   c  or the button  27   d  again, the adjustment level of the selected parameter may be increased or decreased. An operation signal from the display setting part  27  is inputted into the system control part  110 , from which the instruction signal is transmitted to the monitor control part  28 , and thereby the brightness and the contrast on the monitor  26  are adjusted. At the time of the adjustment, the brightness and the contrast may be adjusted to be brought in a state desired by the examiner through observation of the displayed image F of the anterior-segment.  
         [0048]     When the button  27   a  is depressed after the adjustment of the brightness and the contrast on the monitor  26 , the screen on the monitor  26  is switched to an original screen, and the respective adjustment values in the eye refractive power measurement mode and the corneal shape measurement mode are stored in the memory  141 . Besides, the memory  141  is a non-volatile memory which maintains its memory even after power supply of the apparatus is shut off.  
         [0049]     In the same way as is described, when the button  27   a  on the display setting part  27  is depressed after switching to the intraocular pressure measurement mode, an environment setting screen in the intraocular pressure measurement mode is displayed on the monitor  26 . Incidentally, at the time of the switching to the intraocular pressure measurement mode, the measurement part  1   a  is moved to an eye E side and the mirror  9  is removed from the front of the nozzle  13 , so that the image of the anterior-segment of the eye E is picked up by the camera  25 , as described above. Also in this case, the button  27   c  or the button  27   d  is depressed to move the cursor  200  to the parameter to be adjusted, and the button  27   b  is depressed to select the parameter. Then, by depressing the button  27   c  or the button  27   d  again, the adjustment level of the selected parameter may be increased or decreased, so that the brightness and the contrast of the image F of the anterior-segment displayed on the monitor  26  may be adjusted to be brought in a desired state. And then, by depressing the button  27   a , the screen on the monitor  26  is switched to an original screen, and the respective adjustment values in the intraocular pressure measurement mode are stored in the memory  141 .  
         [0050]     Incidentally, it is preferable that the brightness and the contrast are adjusted while checking the respective images F of the anterior-segment picked up by the cameras  25  and  54 , but a model eye may substitute for the eye E for the check.  
         [0051]     After the adjustment as described above is performed, according to the signals for switching to the eye refractive power measurement mode, the corneal shape measurement mode and the intraocular pressure measurement mode, the system control part  110  controls to read from the memory  141  the respective adjustment values of the brightness and the contrast corresponding to the respective modes, and input the instruction signals based on the adjustment values into the monitor control part  28 . The monitor control part  28  controls to adjust and set the brightness and the contrast based on the inputted instruction signals, and thereby the examiner may easily observe the images of the anterior-segment suitable for the respective modes. If the images of the anterior-segment in the eye refractive power measurement mode, the corneal shape measurement mode and the intraocular pressure measurement mode are brought in a state where they may be observed under the similar brightness and the similar contrast, an uncomfortable feeling caused when the modes are switched is lessen, so that the images of the anterior-segment are easily observed at the time of the respective measurements.  
         [0052]     Incidentally, a constitution may be employed, where a control circuit for adjusting respective gains of the image signals outputted from the cameras  25  and  54  is provided instead of the monitor control part  28 .  
         [0053]     Further, as a modified embodiment for adjusting the brightness of the image of the anterior-segment, a constitution may be employed where the light intensity of the light sources  20  is adjusted. In this case, intensity of illumination light in the respective modes is adjusted by a light-intensity adjustment switch in the switch part  121 , and its adjustment values are stored in the memory  141 . In the same way as is described, according to the signals for switching to the respective modes, the system control part  110  controls to read the adjustment values of the light intensity corresponding to the respective modes, and to adjust the light intensity of the light sources  20 . Light-intensity adjustment as such may be performed not only by adjusting luminescence intensity of the light sources themselves, but also by adjusting the number of the light sources to light.  
         [0054]      FIG. 6  is a schematic configuration of a partially modified embodiment of the optical systems arranged inside the main body  1 . Components having the same numeral references as those in  FIG. 3  have basically the same constitutions. In the modified embodiment, a constitution is employed, where a part of the observation optical system including the camera  25  in the measurement part  1   a  is used also at the time of the eye refractive power measurement. In the eye refractive power measurement mode, the air blowing mechanism  102  is removed from the optical axis L 1  by a moving mechanism  105  so that measurement light is not shaded by the air blowing mechanism  102 . An eye refractive power measurement optical system  101  is disposed on an optical path bifurcated by a beam splitter  29 . At the time of the eye refractive power measurement, the eye E is fogged by moving the fixation target  36 . The constitution is such that the light sources for alignment is used also at the time of the eye refractive power measurement; however, dedicated light sources may be prepared instead. The respective alignment states at the time of the eye refractive power measurement and the intraocular pressure measurement are detected by the camera  25  used in both the measurements.  
         [0055]     In this constitution, as the air blowing mechanism  102  is disposed on the optical axis L 1  at the time of the intraocular pressure measurement, the observation optical system to the camera  25  partly differs from that at the time of the eye refractive power measurement. In other words, at the time of the intraocular pressure measurement, the nozzle  13  included in the air blowing mechanism  102 , the two glass plates  14  holding the nozzle  13 , and the glass plate  15  behind them are disposed. The glass plate  14  holding the nozzle  13  arranged at the front end is usually in a size of the order of 10 mm to avoid contact of the nozzle  13  with a face part around the eye E. In contrast, at the time of the eye refractive power measurement, the optical system included in the air blowing mechanism  102  is removed from the optical axis L 1 , so that a measurement window for eye refractive power measurement may take up a larger space. In such a case, the brightness of the image of the anterior-segment picked up by the camera  25  at the time of the intraocular pressure measurement and displayed on the monitor  26  is darker than that at the time of the eye refractive power measurement; however, if the brightness and the contrast are respectively adjusted at the time of the eye refractive power measurement and the intraocular pressure measurement as described above, the images of the anterior-segment become easy to be observed at the time of the respective measurements.  
         [0056]     The above description has been made taking the multifunction apparatus for performing the intraocular pressure measurement, the eye refractive power measurement and the corneal shape measurement as an example; however, the present invention may be applied to other multifunction apparatuses which perform various kinds of examination, measurement, photographing and the like, such as a multifunction apparatus for performing the intraocular pressure measurement and fundus photographing, and a multifunction apparatus for performing the eye refractive power measurement and sectional photographing of the anterior-segment of the eye.  
         [0057]     The foregoing description of the preferred embodiments of the invention has been presented for purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise form disclosed, and modifications and variations are possible in the light of the above teachings or may be acquired from practice of the invention. The embodiments chosen and described in order to explain the principles of the invention and its practical application to enable one skilled in the art to utilize the invention in various embodiments and with various modifications as are suited to the particular use contemplated. It is intended that the scope of the invention be defined by the claims appended hereto, and their equivalents.