JP6052445B2 - Intraocular lens power determination device and program - Google Patents

Description

  The present invention relates to an apparatus and a program for determining the power of an intraocular lens that determines the power of an intraocular lens inserted into the eye by cataract surgery.

  In cataract surgery, in order to determine (calculate) the power (hereinafter referred to as power) of an intraocular lens (hereinafter referred to as IOL) inserted into the eye of the eye after removal of the lens nucleus, the eye is measured and corneal refraction is measured. Subject-specific eye characteristic data such as force and axial length are obtained. Based on this, the frequency of the IOL is calculated according to the IOL calculation formula created by experience or logic. As the IOL calculation formula, an SRK formula, an SRK / T formula, and the like are well known (see Patent Document 1).

  In each IOL calculation formula, a predetermined lens constant (for example, A constant) is used. The lens constant is determined in terms of design for each IOL model (model number) by the IOL manufacturer.

Special table 2007-505716

  However, the portion of the IOL calculation formula that calculates the predicted anterior chamber depth is based on clinical data, and the calculated IOL frequency may be inaccurate for an eye that deviates from the standard eyeball shape.

  Taking the SRK / T formula as an example, the value of the predicted postoperative anterior chamber depth is calculated by a calculation formula derived based on a lot of clinical data. In the SRK / T equation, when calculating the expected postoperative anterior chamber depth, the A constant, the corneal curvature radius, and the axial length are calculated. It is calculated by adding the terms obtained empirically based on it. However, in the conventional method as described above, an error may increase with respect to the predicted postoperative anterior chamber depth, which causes an error in the IOL frequency.

  In view of the above problems, an object of the present invention is to provide an apparatus and a program that can determine an IOL frequency with high accuracy.

  In order to solve the above problems, the present invention is characterized by having the following configuration.

(1) An intraocular lens power determination device that detects reflection from the anterior ocular segment of the eye to be examined and acquires an anterior ocular segment tomographic image to obtain three-dimensional anterior ocular segment data; Obtaining the offset distance from the front of the lens to the contact point of the chin zonule and the lens based on the lens front curvature and the lens rear curvature for each meridian direction in the three-dimensional anterior segment data acquired by the anterior segment imaging device, A frequency calculation unit that calculates the predicted post-operative anterior chamber depth by adding the offset distance to the anterior chamber depth of the eye, and calculates the frequency of the intraocular lens using the predicted post-operative anterior chamber depth. Features.
(2) An intraocular lens power determination program that is executed in a control device that controls the operation of the intraocular lens power determination device, and is acquired by the anterior ocular segment imaging device by being executed by the processor of the control device. A first step for obtaining an offset distance from the front surface of the lens to the contact point of the chin band and the lens based on the front lens surface curvature and the rear lens surface curvature in each meridian direction in the three-dimensional anterior segment data; A second step of calculating the predicted postoperative anterior chamber depth by adding the offset distance obtained in the first step, and using the predicted postoperative anterior chamber depth calculated in the second step of the intraocular lens The third step of performing power calculation is executed by the intraocular lens power determination device.

  According to the present invention, it is possible to determine the IOL frequency with high accuracy.

  Embodiments according to the present invention will be described below with reference to the drawings. FIG. 1 is a schematic configuration diagram showing an optical system of an intraocular lens power determination system 200 according to the present embodiment. The following optical system is built in a housing (not shown). Further, the casing is three-dimensionally moved relative to the eye E via an operation member (for example, a joystick) by driving a known alignment moving mechanism. In the following description, in this embodiment, the axial direction of the subject's eye (eye E) will be described as the Z direction, the horizontal direction as the X direction, and the vertical direction as the Y direction. The surface direction of the fundus may be considered as the XY direction.

  In the following description, an intraocular lens power determination system 200 including an optical coherence tomography device (OCT device) 5, an axial length measuring device 10, and a corneal shape measuring device 300 will be described as an example.

  The OCT device 5 is used as an anterior segment imaging device for capturing a cross-sectional image of the eye E. The axial length measuring device 10 is used for measuring the axial length measurement of the eye E. The corneal shape measuring device 300 is used for measuring the corneal shape. The OCT device 5 will be described taking an optical coherence tomography device for anterior segment tomographic image (cross-sectional image) imaging as an example.

  The OCT device 5 includes an interference optical system (OCT optical system) 100. The OCT optical system 100 irradiates the eye E with measurement light. The OCT optical system 100 detects the interference state between the measurement light reflected from the anterior eye part (for example, a crystalline lens) and the reference light by the light receiving element (detector 120). The OCT optical system 100 includes an irradiation position changing unit (for example, the optical scanner 108) that changes the irradiation position of the measurement light on the anterior eye part in order to change the imaging position on the anterior eye part. The control unit 80 controls the operation of the irradiation position changing unit based on the set imaging position information, and acquires a tomographic image based on the light reception signal from the detector 120.

  The OCT optical system 100 has a so-called ophthalmic optical tomography (OCT) apparatus configuration. The OCT optical system 100 splits the light emitted from the measurement light source 102 into measurement light (sample light) and reference light by a coupler (light splitter) 104. Then, the OCT optical system 100 guides the measurement light to the anterior segment by the measurement optical system 106 and guides the reference light to the reference optical system 110. Thereafter, the detector (light receiving element) 120 receives the interference light obtained by combining the measurement light reflected by the anterior eye part and the reference light.

  The light emitted from the light source 102 is split into a measurement light beam and a reference light beam by the coupler 104. Then, the measurement light flux passes through the optical fiber and is then emitted into the air. The luminous flux is condensed on the anterior eye via the optical scanner 108 and other optical members of the measurement optical system 106. Then, the light reflected by the anterior segment is returned to the optical fiber through a similar optical path.

  The optical scanner 108 scans the measurement light on the eye E in the XY direction (transverse direction). The optical scanner 108 is, for example, two galvanometer mirrors, and the reflection angle thereof is arbitrarily adjusted by the drive mechanism 109.

  Thereby, the reflection (advance) direction of the light beam emitted from the light source 102 is changed, and the light beam 102 is scanned in an arbitrary direction on the eye E. Thereby, the imaging position on the anterior segment is changed. The optical scanner 108 may be configured to deflect light. For example, in addition to a reflective mirror (galvano mirror, polygon mirror, resonant scanner), an acousto-optic device (AOM) that changes the traveling (deflection) direction of light is used.

  The reference optical system 110 generates reference light that is combined with reflected light acquired by reflection of measurement light by the eye E. The reference optical system 110 may be a Michelson type or a Mach-Zehnder type. The reference optical system 110 is formed by, for example, a reflection optical system (for example, a reference mirror), and reflects light from the coupler 104 back to the coupler 104 by being reflected by the reflection optical system and guides it to the detector 120. As another example, the reference optical system 110 is formed by a transmission optical system (for example, an optical fiber), and guides the light from the coupler 104 to the detector 120 by transmitting the light without returning.

  The reference optical system 110 has a configuration in which the optical path length difference between the measurement light and the reference light is changed by moving an optical member in the reference optical path. For example, the reference mirror is moved in the optical axis direction. The configuration for changing the optical path length difference may be arranged in the measurement optical path of the measurement optical system 106.

  The detector 120 detects an interference state between the measurement light and the reference light. In the case of Fourier domain OCT, the spectral intensity of the interference light is detected by the detector 120, and a depth profile (A scan signal) in a predetermined range is obtained by Fourier transform on the spectral intensity data. Here, the control unit 80 can acquire a tomographic image by scanning the measurement light in the predetermined transverse direction on the anterior segment by the optical scanner 108. That is, an anterior tomographic image of the eye to be examined is captured. For example, by scanning in the X direction or the Y direction, a tomographic image (anterior segment tomographic image) on the XZ plane or the YZ plane of the anterior segment of the eye to be examined can be acquired (in this embodiment, measurement is performed in this way. (The method of performing one-dimensional scanning of light with respect to the anterior segment and obtaining a tomographic image is B scan). The acquired anterior segment tomogram is stored in the memory 85 connected to the control unit 80. Furthermore, it is also possible to acquire a three-dimensional image of the anterior segment of the eye to be examined by two-dimensionally scanning the measurement light in the XY direction.

  For example, examples of the Fourier domain OCT include Spectral-domain OCT (SD-OCT) and Swept-source OCT (SS-OCT). Moreover, Time-domain OCT (TD-OCT) may be used.

  In the case of SD-OCT, a low-coherent light source (broadband light source) is used as the light source 102, and the detector 120 is provided with a spectroscopic optical system (spectrum meter) that separates interference light into each frequency component (each wavelength component). . The spectrum meter includes, for example, a diffraction grating and a line sensor.

  In the case of SS-OCT, a wavelength scanning light source (wavelength variable light source) that changes the emission wavelength at a high speed in time is used as the light source 102, and a single light receiving element is provided as the detector 120, for example. The light source 102 includes, for example, a light source, a fiber ring resonator, and a wavelength selection filter. Examples of the wavelength selection filter include a combination of a diffraction grating and a polygon mirror, and a filter using a Fabry-Perot etalon.

  The corneal shape measuring device 300 is roughly divided into a kerato projection optical system 50, an alignment projection optical system 40, and an anterior ocular segment front imaging optical system 30.

  The kerato projection optical system 50 has a ring-shaped light source 51 arranged around the measurement optical axis L1, and measures a corneal shape (curvature, astigmatic axis angle, etc.) by projecting a ring index on the eye cornea to be examined. Used for. As the light source 51, for example, an LED that emits infrared light or visible light is used. In addition, about the projection optical system 50, at least 3 or more point light sources should just be arrange | positioned on the same periphery centering on the optical axis L1, and may be an intermittent ring light source. Further, it may be a placido index projection optical system that projects a plurality of ring indexes.

  The alignment projection optical system 40 is disposed inside the light source 51, has a projection light source 41 (for example, λ = 970 nm) that emits infrared light, and is used to project an alignment index onto the eye cornea Ec to be examined. And the alignment parameter | index projected on the cornea Ec is used for position alignment (for example, automatic alignment, alignment detection, manual alignment, etc.) with respect to the eye to be examined. In the present embodiment, the projection optical system 50 is an optical system that projects a ring index on the subject's cornea Ec, and the ring index also serves as a Mayer ring. Further, the light source 41 of the projection optical system 40 also serves as anterior segment illumination that illuminates the anterior segment with infrared light from an oblique direction. The projection optical system 40 may further include an optical system that projects parallel light on the cornea Ec, and the front-rear alignment may be performed by a combination with the finite light by the projection optical system 40.

  The anterior segment front imaging optical system 30 is used to capture (acquire) an anterior segment front image. The anterior segment front imaging optical system 30 includes a dichroic mirror 33, an objective lens 47, a dichroic mirror 62, a filter 34, an imaging lens 37, and a two-dimensional imaging device 35, and captures an anterior segment front image of the eye to be examined. Used for. The two-dimensional imaging device 35 is disposed at a position substantially conjugate with the anterior eye portion to be examined.

  The anterior ocular segment light reflected by the projection optical system 40 and the projection optical system 50 is imaged on the two-dimensional imaging device 35 via the dichroic mirror 33, the objective lens 47, the dichroic mirror 62, the filter 34, and the imaging lens 37. The

  The axial length measuring device 10 includes a light projecting optical system and a light receiving optical system, and the light projecting optical system includes a measurement light source 1 that emits low-coherent light. Then, the light emitted from the light source 1 is divided into measurement light and reference light, and at least the measurement light is irradiated to the eye to be examined, and the reflected light from the eye to be examined and the reference light are combined and made incident on the light receiving element. Based on the light reception signal output from the light receiving element, the axial length is calculated based on the timing when the interference light is detected by the light receiving element. In the present embodiment, the measurement light source of the axial length measurement optical system 10 also serves as a fixation lamp.

  Further, for example, most of the fundus reflection light acquired by the reflection of the light emitted from the light source 1 on the fundus is transmitted through the dichroic mirror 33 and received by the light receiving element of the axial length measurement optical system 10. A part of the fundus reflection light is reflected by the dichroic mirror 33 and imaged by the anterior ocular segment imaging optical system 30.

  Next, the control system will be described. The control unit 80 controls the entire apparatus and calculates measurement results. The control unit 80 is connected to each member of the OCT device 5, each member of the axial length measuring device 10, each member of the corneal shape measuring device 300, the monitor 70, the operation unit 84, the memory 85, and the like.

  In the present embodiment, an axial length measurement mode for measuring an axial length and an anterior segment measurement mode for measuring an anterior segment (for example, a corneal shape) from an anterior segment sectional image are prepared. Each mode is switched automatically or manually.

  The operation unit 84 may be a general-purpose interface such as a mouse as an operation input unit, or may be a touch panel. The operation unit 84 is, for example, a mode for switching between an axial length measurement mode for measuring an axial length and an anterior segment measurement mode for measuring an anterior segment (eg, corneal shape) from an anterior segment cross-sectional image. A changeover switch 84a is provided.

  In addition to the various control programs, the memory 85 stores a software program for the controller 80 to calculate the axial length / corneal shape, and a software program for the controller 80 to calculate the IOL frequency. Yes.

<Anterior segment measurement mode>
The operation of the apparatus having the above configuration will be described. In the following description, the anterior segment measurement mode will be described. While looking at the alignment state of the eye to be examined displayed on the monitor 70, the examiner moves the apparatus up and down, left and right, and in the front-rear direction using an operation means such as a joystick (not shown), and moves the apparatus to the eye E to be determined. Put it in the positional relationship. In this case, the examiner fixes the fixation target to the eye to be examined.

  FIG. 2 is a diagram illustrating an anterior ocular segment observation screen on which an anterior ocular segment image captured by the image sensor 35 is displayed. At the time of alignment, the light source 41 and the light source 51 are turned on. Further, the light source 102 of the OCT device 5 is turned on. Here, as shown in FIG. 2, the examiner performs vertical and horizontal alignment so that the electronically displayed reticle LT and the ring index R1 by the light source 41 are concentric. In addition, the examiner performs front-rear alignment so that the ring index R1 is in focus. A ring index R2 from the light source 51 is displayed outside the ring index R1.

  When the alignment with respect to the anterior segment is completed, the controller 80 acquires a tomographic image by the OCT optical system 100 based on a preset scanning pattern, and displays the acquired tomographic image on the monitor 75 as a moving image. .

  First, corneal shape measurement is performed. In the present embodiment, the corneal curvature radius on the front surface of the cornea is calculated using the corneal shape measuring device 300, and the corneal curvature radius on the rear surface of the cornea is calculated using the OCT device 5. When alignment is performed as described above and a predetermined trigger signal is generated, the control unit 80 captures an anterior segment image. Then, the control unit 80 determines the corneal shape of the eye to be examined (for example, the corneal curvature of the front surface of the cornea in the strong main meridian direction and the weak main meridian direction) based on the ring index images R1 and R2 in the anterior segment image stored in the memory 85. Radius, corneal astigmatic axis angle, etc.) are calculated, and the measurement results are stored in the memory 85.

  Next, an anterior ocular segment image is taken. The control unit 80 acquires an anterior segment tomogram and stores the acquired image data (for example, as a still image) in the memory 85. The anterior segment tomogram acquired by the OCT optical system 100 can capture a tomogram in the range up to the rear surface of the crystalline lens. For this reason, the control unit 80 processes (analyzes) the acquired anterior segment tomogram, and in this embodiment (in this embodiment, the corneal curvature radius of the posterior cornea, the anterior chamber depth, the corneal thickness, the front surface of the lens) Curvature, lens back surface curvature, lens thickness).

  In the present embodiment, a position where the corneal apex position and the optical axis (L1) of the apparatus coincide with each other is set as a reference position for alignment, and alignment is performed. That is, the scanning position for acquiring the anterior segment tomogram is aligned so that the scanning position passes through the corneal apex position.

<Axial length measurement>
Next, the axial length measurement mode will be described. While looking at the alignment state of the eye to be examined displayed on the monitor 70, the examiner moves the apparatus up and down, left and right, and in the front-rear direction using an operation means such as a joystick (not shown), and moves the apparatus to the eye E to be determined. Put it in the positional relationship.

  After the alignment is completed, a trigger signal for starting measurement is automatically or manually output, and when the measurement light source 1 is turned on by the control unit 80, the measurement light is irradiated to the eye to be examined by the axial length measuring device 10, and measurement is performed. Reflected light from the eye to be examined by light is incident on the light receiving element of the axial length measuring device 10. Based on the light reception signal output from the light receiving element, the axial length is calculated based on the timing when the interference light is detected by the light receiving element.

<IOL frequency calculation>
As described above, when the measurement in the axial length measurement mode and the anterior segment measurement mode is completed, the control unit 80 calculates the IOL frequency based on the acquired measurement data.

  As a method for calculating the IOL frequency, a part of the known SRK / T formula, Binkhors formula, etc. is used. For example, when the SRK / T formula is used, the IOL power calculation is performed using parameters of the corneal curvature radius, the axial length, and the lens constant (referred to as A constant when using the SRK / T formula).

  The control unit 80 obtains an offset distance from the front surface of the lens to the contact point of the chin band and the lens based on the anterior segment cross-sectional image acquired by the OCT device 5, and predicts by adding the offset distance to the anterior chamber depth of the eye The postoperative anterior chamber depth is calculated, and the intraocular lens power is calculated using the predicted postoperative anterior chamber depth.

  Specifically, using FIG. 3, first, the corneal height from the front of the cornea to the front of the crystalline lens is calculated from the corneal thickness CCT and the anterior chamber depth ACD, and the offset amount (offset distance) with respect to the corneal height. An expected postoperative anterior chamber depth ELP is calculated by adding a correction amount α (a function of an A constant) that varies depending on the types of X and IOL. Then, the IOL frequency is calculated using the predicted postoperative anterior chamber depth ELP, the axial length measurement result AL, and the corneal curvature radius.

  The offset amount X indicates a distance from the position of the front surface of the crystalline lens after the IOL is inserted to the position of the IOL support portion (approximately the position of the optical portion of the IOL). Note that the offset amount X is excluded without considering the amount of movement of the IOL toward the posterior lens capsule (the correction amount α shown above) that occurs when the IOL receives pressure from the lens capsule. Will be described later). The position of the IOL support portion is the same as the position of the contact portion between the chin band and the crystalline lens (for example, the intersection of the crystalline lens front surface and the crystalline lens rear surface).

  Here, since the cornea thickness CCT and the anterior chamber depth ACD are measurement results, errors are unlikely to occur. However, when the offset amount X is determined mainly by the A constant, which is a parameter based on a lot of clinical data, the error does not occur. Prone to occur.

  A method for calculating the offset amount X with higher accuracy will be described below. In this embodiment, the control unit 80 includes, as the morphological information of the eye lens to be examined, lens front surface information (lens front surface radius of curvature) R3, lens rear surface information (lens rear surface radius of curvature) R4, lens thickness information (lens thickness) LT. Form information including at least one of them is obtained, and an offset distance is calculated based on the acquired form information. That is, in order to accurately calculate the offset amount X, it is necessary to obtain a crystalline lens profile according to the eye to be examined.

  First, the position of the contact portion between the chin band and the crystalline lens is calculated using the crystalline lens front surface curvature radius R3, the crystalline lens rear surface curvature radius R4, and the crystalline lens thickness LT. Since the position of the contact portion between the chin zonule and the crystalline lens is a portion where the support portion of the IOL is located when the IOL is inserted, by calculating the position of the contact portion between the chin zonule and the crystalline lens, postoperatively The position of the IOL support part can be calculated. And since the position of the IOL support part after an operation is handled about the same as the position of the IOL, the position of the IOL can be calculated by calculating the position of the IOL support part after the operation. Thereby, the offset amount X can be calculated.

  Specifically, the offset amount X can be obtained as follows. FIG. 4 is a diagram illustrating a method for calculating the offset amount X. h represents the distance from the optical axis L1 to the contact portion between the lens chin belt and the lens. X1 indicates the distance from the lens front surface curvature center O4 to the lens rear surface on the optical axis L1. X1 ′ represents the distance from the contact position between the lens chin belt and the lens to the rear surface of the lens. X2 indicates the distance from the lens back surface curvature center O3 to the lens front surface in the optical axis L1. X represents the distance from the contact position between the lens chin belt and the lens to the front surface of the lens, and is an offset amount.

  First, the following equation holds according to Pythagorean theorem.

And in said formula, since h is the same, when these formulas are developed, the following formula is established.

That is, since the offset amount X is calculated using the actually measured value, the offset amount X with less error can be calculated.

  Next, the predicted postoperative anterior chamber depth ELP is calculated from the calculated offset amount X. The predicted postoperative anterior chamber depth ELP is calculated based on the offset amount X, the anterior chamber depth ACD, the corneal thickness CCT, and the correction amount α.

  As shown in FIG. 5, the correction amount α is a parameter for correcting the amount of movement of the IOL when the IOL is pushed down to the posterior capsule side by the pressure of the lens capsule after insertion of the IOL. When the IOL is pushed down toward the posterior capsule, the IOL moves slightly toward the posterior capsule. That is, the expected postoperative anterior chamber depth ELP can be calculated with higher accuracy by correcting the amount of movement of the IOL toward the posterior capsule side and calculating the predicted postoperative anterior chamber depth ELP. The correction amount α is calculated by a well-known function using an A constant set according to the type of the IOL because the movement amount varies depending on the IOL structure, material, and the like. That is, the predicted postoperative anterior chamber depth is corrected by an A constant specific to each intraocular lens. The A constant is set in advance and stored in the memory 85.

  The expected postoperative anterior chamber depth ELP can be determined as follows.

As described above, the actual post-operative anterior chamber depth ELP with high accuracy is calculated by adding the actual measurement value such as the lens shape information and calculating the offset amount X. Then, the IOL frequency can be accurately calculated using the predicted postoperative anterior chamber depth ELP and the axial length measurement result AL.

  Further, the present invention calculates the corneal curvature and corneal thickness of the front and back surfaces of the cornea, and calculates the IOL frequency from the actual measurement values, so it can be accurately applied to an eye to be examined having a change or abnormality in the corneal shape. The IOL frequency can be calculated. For example, since the IOL frequency is calculated in a state in which changes in the corneal shape (corneal curvature, corneal thickness) are taken into consideration for the subject's eye in which the corneal shape has changed, such as the eye after LASIK surgery, Especially useful.

  In the optical coherence tomography device for photographing an anterior ocular segment tomogram (cross-sectional image), the present invention can also obtain a three-dimensional shape image by acquiring an anterior ocular segment tomogram at a plurality of scanning positions. Applicable. The OCT device 5 is an anterior segment imaging device that acquires a three-dimensional sectional image (three-dimensional anterior segment data) of the anterior segment, and the control unit 80 is a three-dimensional section acquired by the anterior segment imaging device. Based on the image, an offset distance from the front of the lens to the contact point between the chin band and the lens is determined three-dimensionally. In this case, the average of the lens front curvature and the lens rear curvature for each meridian direction in the three-dimensional anterior segment data is calculated, and ELP is calculated based on this. And by acquiring a measured value from a three-dimensional shape image, the accuracy of the acquired measured value improves.

  In the present embodiment, an optical coherence tomography device for photographing an anterior ocular segment tomographic image (cross-sectional image) is taken as an example of the anterior ocular segment imaging device that captures an anterior segment cross-sectional image, but the present invention is not limited thereto. A light projecting optical system that projects light emitted from a light source toward the anterior eye portion of the eye to be examined and forms a light cutting surface on the anterior eye portion, and before being acquired by scattering at the anterior eye portion of the light cutting surface. And a light receiving optical system having a detector that receives light including scattered light of the eye part, and any structure that forms an anterior ocular segment image based on a detection signal from the detector may be used. That is, the present invention can be applied to an apparatus or the like that projects slit light on the anterior segment of the optometer and obtains a cross-sectional image of the anterior segment by a Shine peak camera.

  Furthermore, the present invention is also applicable to an apparatus that acquires a three-dimensional shape image of the anterior eye segment by rotating a Shine peak camera. In this case, it is possible to acquire the three-dimensional shape image of the anterior segment with high accuracy by performing the deviation correction for each predetermined rotation angle, and the accuracy of the measurement value acquired from the three-dimensional shape image is improved. In this case, a positional deviation in a direction perpendicular to the imaging surface (slit cross section) is detected, and a deviation correction process is performed based on the detection result.

  Moreover, in the said structure, although the anterior ocular segment cross-sectional image was acquired optically, it is not limited to this. Any anterior ocular segment imaging device that detects an anterior ocular segment cross-sectional image by detecting reflection from the anterior ocular segment to be examined. For example, what is necessary is just a structure which acquires the anterior ocular segment cross-section image by detecting the reflection information from an anterior ocular segment using the ultrasonic probe for B scan.

  In the present embodiment, a known IOL calculation formula such as an SRK / T formula or a Binkhors formula is used as a method for calculating the IOL frequency, but the present invention is not limited to this. For example, the IOL frequency can also be calculated by a ray tracing method that uses light rays to geometrically follow light reflection and refraction and simulate the behavior of light. In this case, the IOL power is calculated by the ray tracing method using the predicted postoperative anterior chamber depth ELP, the corneal thickness CCT, the axial length measurement result AL, the corneal curvature radius of the anterior cornea, and the corneal curvature radius of the posterior cornea. Since the ray tracing method calculates the IOL frequency by simulation of light reflection and refraction, the IOL frequency can be calculated with high accuracy by the IOL calculation formula which is a theoretical formula.

  In the present embodiment, the corneal curvature measuring device 300 is used to calculate the corneal curvature radius on the front surface of the cornea, and the OCT device 5 is used to calculate the corneal curvature radius on the rear surface of the cornea. It is not limited. The OCT device 5 may calculate the corneal curvature radius on the front and back surfaces of the cornea. Moreover, you may handle the corneal curvature radius of the cornea front-back surface with the same measured value. That is, the corneal curvature radius in the front surface of the cornea calculated by the corneal shape measuring device 300 is used as the corneal curvature radius in the front and back surfaces of the cornea.

  In the present embodiment, corneal topography can also be used as the corneal shape measuring device 300. In this case, when calculating the curvature radius of the front surface of the cornea, the curvature radius of the front surface of the cornea is calculated from the entire shape of the cornea, so that the curvature radius of the front surface of the cornea is calculated with high accuracy. For this reason, when calculating the IOL frequency, the accuracy of the IOL frequency calculation is improved.

  In the present embodiment, the control unit 80 processes the anterior segment cross-sectional image acquired by the OCT device 5 to obtain the morphological information of the eye lens to be examined, and the offset distance X based on the obtained morphological information. However, the present invention is not limited to this.

  When the OCT device 5 is an anterior ocular segment imaging device (for example, an ultrasonic B probe, an anterior ocular segment OCT) capable of imaging a cross-sectional image of the anterior ocular segment including the ciliary body, the control unit 80 controls the OCT device 5. The offset distance X is obtained based on the position information of the ciliary body in the cross-sectional image of the anterior segment acquired by the above. For example, the ciliary body (the ciliary body tip) is detected from the acquired anterior segment tomogram (anterior segment cross-sectional image), and the chin band position is predicted from the detected ciliary body position. Then, the position of the contact portion between the chin band and the lens may be detected from the predicted chin band position.

  Further, when the OCT device 5 is an anterior ocular segment imaging device (for example, an ultrasonic B probe, an anterior ocular segment OCT) capable of imaging a cross-sectional image of the anterior ocular segment including a contact portion between the chin zonule and the crystalline lens, control is performed. The unit 80 processes the contact portion in the anterior segment cross-sectional image acquired by the OCT device 5 to obtain the offset distance X. For example, when a chin zonule is photographed in the anterior segment tomogram (cross-sectional image), the position of the contact portion between the chin zonule and the crystalline lens may be detected from the acquired anterior segment tomogram. .

  Note that the present invention is not limited to the apparatus described in this embodiment. For example, IOL frequency calculation software (program) that performs the functions of the above embodiments is supplied to a system or apparatus via a network or various storage media. A computer of the system or apparatus (for example, a CPU) can also read and execute the program.

It is a schematic block diagram explaining the structure of the intraocular lens power determination apparatus which concerns on this embodiment. It is a figure which shows the anterior ocular segment observation screen on which the imaged anterior segment image was displayed. It is a figure for demonstrating calculation of IOL frequency. It is a figure explaining the calculation method of offset amount X. FIG. It is a figure explaining the corrected amount (alpha).

DESCRIPTION OF SYMBOLS 5 Optical coherence tomography device 10 Axial length measurement device 30 Anterior ocular segment front imaging optical system 40 Alignment projection optical system 50 Kerato projection optical system 70 Monitor 80 Control unit 85 Memory 84 Operation unit

Claims (4)

An intraocular lens power determination device,
An anterior ocular segment imaging device that obtains three-dimensional anterior segment data by detecting reflection from the anterior segment of the eye to be examined and acquiring an anterior segment tomographic image;
Obtaining the offset distance from the front of the lens to the contact point of the chin zonule and the lens based on the lens front curvature and the lens rear curvature for each meridian direction in the three-dimensional anterior segment data acquired by the anterior segment imaging device, A frequency calculation unit that calculates a predicted postoperative anterior chamber depth by adding the offset distance to the anterior chamber depth of the eye, and calculates the frequency of the intraocular lens using the predicted postoperative anterior chamber depth;
An intraocular lens power determination device comprising: The intraocular lens power determination apparatus according to claim 1, wherein the power calculation unit calculates the power of the intraocular lens by a ray tracing method using the predicted postoperative anterior chamber depth. The frequency calculation unit obtains an offset distance from the front surface of the lens to the contact point of the chin zonule and the lens based on an average of the front lens surface curvature and the rear lens surface curvature for each meridian direction in the three-dimensional anterior segment data. The intraocular lens power determination apparatus according to claim 1 or 2. An intraocular lens power determination program executed in a control device that controls the operation of the intraocular lens power determination device,
By being executed by the processor of the control device,
A first step of obtaining an offset distance from the front surface of the lens to the contact point of the chin band and the lens based on the front lens surface curvature and the rear lens surface curvature in each meridian direction in the three-dimensional anterior segment data acquired by the anterior segment imaging device. When,
A second step of calculating a predicted postoperative anterior chamber depth by adding the offset distance determined in the first step to the anterior chamber depth of the eye;
A third step of calculating the power of the intraocular lens using the predicted postoperative anterior chamber depth calculated in the second step;
Is executed by the intraocular lens power determining apparatus.