CN210114570U - Imaging mode and treatment mode automatic switching device of fundus laser treatment device - Google Patents
Imaging mode and treatment mode automatic switching device of fundus laser treatment device Download PDFInfo
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- CN210114570U CN210114570U CN201920578272.8U CN201920578272U CN210114570U CN 210114570 U CN210114570 U CN 210114570U CN 201920578272 U CN201920578272 U CN 201920578272U CN 210114570 U CN210114570 U CN 210114570U
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Abstract
The utility model discloses an image forming mode and treatment mode automatic switching control equipment of fundus laser therapy device, include: a high-level conducting point A is arranged, a light emitting diode LED and a resistor which is connected in series by a resistor R1 and a resistor R2 are connected between the conducting point B and the working ground in parallel, and a conducting point C between the resistor R1 and the resistor R2 is connected to a chip pin of which the detection input end is high level or low level; the fundus laser treatment device is switched to a treatment mode or an imaging mode by controlling the conduction points A and B to be switched on or off. Adopt the utility model discloses, can make eye ground laser therapy device automatic switch-over between formation of image mode, treatment mode.
Description
Technical Field
The utility model relates to an eye ground laser imaging and treatment technique especially relates to an imaging mode and treatment mode automatic switching control equipment of eye ground laser therapy device.
Background
Diabetic Retinopathy (DR) is the leading blinding disease in the working age group. The main causes of visual impairment and blindness in patients with DR are Proliferative Diabetic Retinopathy (PDR) and Diabetic Macular Edema (DME), while laser photocoagulation is the leading treatment for patients with Diabetic Retinopathy (DR).
Currently, fundus laser therapy techniques for patients with Diabetic Retinopathy (DR) and patients with macular degeneration and other ophthalmic diseases mainly rely on doctors to perform fixed-point striking by manually operating laser or perform striking by using two-dimensional galvanometer to perform laser in an array shape. However, these techniques are often not accurate enough, and the treatment measures are based on mechanical contact, so that the operation time is long, and the experience of the clinician and the patient is poor (for example, DME is increased to cause the side effects of permanent central vision impairment, laser scar enlargement and the like, and peripheral vision, visual field reduction and dark vision reduction of the patient are caused). In addition, the existing methods of manual fundus laser surgery or dot matrix laser striking with a scanning galvanometer for treatment cannot realize automatic and intelligent laser fundus surgery. But also cannot check and check the treatment effect in real time, so the efficiency is not high.
At present, the laser treatment target imaging mode and the laser treatment mode of the eyeground cannot be automatically switched in the eyeground laser treatment device/system.
SUMMERY OF THE UTILITY MODEL
In view of this, the main objective of the present invention is to provide an automatic switching device for imaging and treatment modes of a fundus oculi laser treatment device, which can automatically switch between the imaging mode and the treatment mode by switching between low and high level signals for the fundus oculi laser treatment device (or treatment system).
In order to achieve the above purpose, the technical scheme of the utility model is realized like this:
an automatic switching device for an imaging mode and a treatment mode of a fundus laser treatment device, the automatic switching device comprising: a high-level conducting point A is arranged, a light emitting diode LED and a resistor which is connected in series by a resistor R1 and a resistor R2 are connected between the conducting point B and the working ground in parallel, and a conducting point C between the resistor R1 and the resistor R2 is connected to a chip pin of which the detection input end is high level or low level; the fundus laser treatment device is switched to a treatment mode or an imaging mode by controlling the conduction points A and B to be switched on or off.
Wherein: the chip is a field programmable logic array FPGA.
The circuit for controlling the conduction or disconnection of the conducting points A and B specifically comprises: arranging a conductive metal sheet on the FC knob of the optical fiber coupler; rotating fiber coupler FC causes conducting point a to be on or off from conducting point B.
When the conductive points A and B are conducted, the LED is lightened, and the conductive point C is at a high level.
When the conductive point a is disconnected from the conductive point B, the conductive point C outputs a low level.
The imaging mode is confocal laser scanning imaging (SLO) or line scanning fundus camera (LSO).
The utility model discloses an imaging and treatment mode automatic switching control equipment of eye ground laser therapy device has following beneficial effect:
the imaging and treatment mode automatic switching device of the eye fundus laser treatment device provides a real-time automatic switching function of an eye fundus image display mode and a laser treatment mode for ophthalmic eye fundus laser surgery, facilitates image acquisition, real-time viewing of target images and rapid switching and real-time imaging under the laser treatment mode, and is convenient for a clinician to confirm that a treatment area is accurate and accurately control laser striking dosage during treatment, thereby being beneficial to realizing the purpose of accurate treatment.
Drawings
FIG. 1 is a schematic view of an intelligent fundus laser surgery treatment system according to an embodiment of the present invention;
fig. 2 is a schematic diagram of a hardware implementation manner of the laser image stabilization and treatment device 1 shown in fig. 1 according to the present invention;
FIG. 3 is a schematic diagram of an exemplary SLO fast scan and slow scan mechanism;
FIG. 4 is a schematic diagram of one implementation of the light splitting device S1 shown in FIG. 2;
FIG. 5 is a schematic view of a manner of achieving fundus tracking in a sawtooth scanning direction by a sawtooth superposition offset;
fig. 6, including fig. 6A and 6B, is a schematic diagram of a mechanism for controlling the mirror M3 according to an embodiment of the present invention;
fig. 7 is a schematic diagram of a two-dimensional scanning method for controlling the scanning spatial position of the OCT on the fundus according to the embodiment of the present invention;
fig. 8 is a schematic diagram of a design manner of a light splitting device S3 corresponding to the auxiliary module light source according to an embodiment of the present invention;
fig. 9 is a schematic diagram of a mechanical and electronic combined device for notifying a user and whether the current auxiliary module of the host control system is the imaging mode 2 or the laser therapy according to the embodiment of the present invention.
Detailed Description
The present invention will be described in further detail with reference to the accompanying drawings and embodiments of the present invention.
Fig. 1 is the embodiment of the utility model discloses intelligence fundus laser surgery treatment system sketch map.
As shown in fig. 1, the intelligent fundus laser surgery treatment system is also an ophthalmological diagnosis and treatment platform. Mainly comprises a laser image stabilizing and treating device 1, a data control device 2 and an image display device 3. Preferably, a data processing device 4 may also be included. Wherein:
the laser image stabilization and treatment device 1 further comprises an imaging diagnosis module 1A and a laser treatment module 1B. As another embodiment, the laser therapy module 1B may be combined with one of the imaging modules (i.e., the second imaging module 12); preferably, hardware can be shared with the second imaging module 12 for cost saving and convenient control.
The laser treatment module 1B comprises a laser output adjusting module 13 and a second imaging module 12; the imaging diagnosis module 1A includes a first imaging module 11 and a coupling module 14.
Specifically, in the present embodiment, the first imaging module 11 is set as a master module (master modules), and the corresponding scanning mirror inside thereof is a master mirrors (master scanners). The second imaging module 12 and the laser output adjusting module 13 (for laser therapy) are set as slave modules (slave scanners), and the corresponding scan mirrors therein are slave scan mirrors (slave scanners). The first imaging module 11 may be a confocal laser scanning imaging (SLO) or a line scanning fundus camera (LSO), or a fundus camera (fundus camera), or an ultra-high definition adaptive fundus imager (AOSLO). The second imaging module 12 may be an Optical Coherence Tomography (OCT) or SLO. Accordingly, the first imaging module 11 and the second imaging module 12 support various imaging module combinations, such as SLO + OCT, fundus camera + SLO, or AOSLO + SLO.
The laser output adjusting module 13 is provided with a built-in zoom lens for adjusting the laser output dosage, and the size of the fundus laser spot can be controlled by changing the position of the zoom lens (zoom lens), so that the clinical operation is facilitated.
The data control device 2 further includes a laser control module 21, an imaging control module 22 and an image data acquisition module 23. Wherein:
the first imaging module 11 and the second imaging module 12 are controlled in real time by the data control device 2 through the imaging control module 22. Further, scanning imaging is performed by a first imaging module 11, such as SLO, LSO, or/and a second imaging module 12, such as OCT, through a galvanometer.
The data control module 2 realizes real-time scanning of the eyeground by adjusting parameters such as clock signals, amplitude, frequency and the like of the system. Meanwhile, the data control module 2 can also control the vibration optics in the first imaging module 11 and the second imaging module 12 simultaneously, and arbitrarily (angularly) change scanning parameters, such as the imaging size, the frame frequency of the image, the image brightness and gray scale control, the image pixel resolution, the dynamic range of the image, and the like. Moreover, the image acquisition can be performed through the data acquisition port of the image data acquisition module 23, and the fundus images of the first imaging module 11 and the second imaging module 12 can be displayed on the image display device 3 in real time, so that a clinician can conveniently perform real-time observation and diagnosis.
Preferably, the clinician can analyze the acquired images in real time and give a relevant reference treatment plan via the data processing device 4. For example: marking out reference treatment areas, giving out a reference laser dose standard corresponding to each area, giving out the laser spot size corresponding to each area, and the like.
Furthermore, the utility model discloses laser image stabilization and treatment device 1 can realize that the eye ground target trails and the locking function, and concrete process is: real-time human eye movement signals (including motion signals x and y) are calculated through fundus image information acquired by the first imaging module 11 and are sent to the data control device 2, the data control device 2 outputs real-time control signals through the imaging control module 22, the position of a galvanometer in the second imaging module 12 is changed, and the galvanometer is locked with a target in real time, so that the purpose of real-time target tracking and locking is achieved. The real-time control signal is calibrated in advance to ensure that the change of the position of the galvanometer is consistent with the actual human eye deviation.
In the embodiment of the present invention, the laser output adjusting module 13 and the second imaging module 12 of the laser treatment apparatus support a common hardware system. The function of integrated work of fundus imaging and laser therapy can also be realized through the cooperation of the couplers.
The data control device 2 can respectively control the fundus oculi target to image and adjust the output of the laser in the laser output adjusting module 13 in real time through the imaging control module 22 and the laser control module 21, including adjusting the output power, the output switch, and the modulation of the output signal.
The laser control module 21 may use two lasers with similar wavelengths, or may use the same laser as both the treatment laser and the reference light. In the present embodiment, the laser light source may be a 532nm CW, or a femtosecond laser system.
After the laser treatment is finished, the clinician can also observe the images of the eyeground of the patient after the treatment in real time through the display screen of the image display device 3, judge the operation result in real time, and upload the images of the eyeground to the patient database document in the data processing device 4, so as to facilitate follow-up observation at the later period.
The embodiment of the utility model provides an example is the eye ground of human eye. The laser image stabilization and treatment device 1 composed of the first imaging module 11, the second imaging module 12, the coupling module 14 and the like can also be used for other different biological tissues, such as intestines and stomach, skin and the like. The following description is still given taking as an example application to the fundus of a human eye.
Fig. 2 is a schematic diagram of a hardware implementation manner of the laser image stabilization and treatment device 1 shown in fig. 1 according to the present invention.
As shown in fig. 2, the laser image stabilization and treatment device can be used as an independent laser fundus navigation and treatment device, and can also be combined with other data control devices to be used as a complete laser surgery treatment system for clinical application.
In fig. 2, the light sources L11, L12, …, and L1n are a plurality of imaging light sources controlled (or modulated) by the control (signals) 11, 12, …, and 1n, respectively, for imaging by the first imaging module 11. For example, infrared light having a wavelength of 780nm is used for fundus reflection imaging, light having a wavelength of 532nm is used for fundus autofluorescence imaging, or a light source of other wavelength bands is employed for other forms of fundus imaging. The plurality of imaging light sources can enter the optical system through the fiber coupling device FC2, and any one of the light sources L11 … L1n can be controlled (or modulated), such as the control signals shown in the main module in fig. 2, i.e., control (signal) 11, …, control (signal) 1 n. The control (or modulation) parameters, including output power, switch state, etc., may also be selectively synchronized or unsynchronized with the scan mirror. The related art of synchronizing with the scanning mirror is described in detail in the previously filed patent application, and is not described herein again.
The imaging light source L11 … L1n transmits through the spectroscopic device S1, passes through the scanning mirror M11 and the scanning mirror M12, passes through the spectroscopic device S2, and enters the bottom of the eye (eye).
Signals returning from the fundus, such as reflected signals from photoreceptor cells, or fluorescence signals from excited proteins in the fundus, or other signals returning from the fundus, are reflected along the same optical path to the beamsplitter S1, and then through another movable beamsplitter S3 to a photodetector, such as an Avalanche PhotoDiode (APD). In the embodiment of the present invention, the APD is described as an example of a photodetector. The photodetector may also be a photomultiplier tube (PMT), CMOS, CCD, or other photodetector device.
In the embodiment of the present invention, the above-mentioned photodetectors (such as APD, PMT, CMOS, CCD) are all provided with a controllable or programmable gain adjustment mechanism, and can be dynamically adjusted by the program control signal of the receiving system host, so as to adapt to different imaging modes, for example, dynamically adjust through the control signal 4 shown in fig. 2.
The set of scanning mirrors M11 and M12 shown in fig. 2 are used primarily for orthogonally scanning fundus imaging positions, with the scanning axes of the scanning mirrors M11 and M12 being typically 90 degrees.
In the case of the first imaging module 11 corresponding to SLO, the scanning mirror M12 of the embodiment of the present invention can be implemented by a two-dimensional tilting mirror (tilting mirror) or two one-dimensional tilting mirrors. In the actual light machine system of the present invention, scanning mirror M12 employs a set of 2-dimensional scanning mirrors 6220H (or 6210H) of Cambridge Technology. 6220H, the first axis, the slow scan axis, is orthogonal to the scan direction of the M11 fast scan axis; 6220H, the second axis, which is not involved in scanning but is used only for target tracking, is parallel to the scanning axis of M11.
In the case of the above-described corresponding SLO, the scan mirror M11 is controlled by the system host as the scan field (scanningfield) of the fast resonant mirror, or is manually controlled.
In the above embodiment, the scanning motion trajectory of M12 orthogonal to M11 is a triangle wave. The amplitude and frequency of the triangular wave, the climbing period and the return period of the triangular wave, and other scanning parameters are controlled by a system host. The amplitude of the triangular wave determines the field size in the slow scan direction, and the frequency of the triangular wave determines the frame rate of the imaging system (see fig. 3).
Fig. 3 is a schematic diagram of a typical SLO fast scan and slow scan mechanism. The fast resonant mirror linearly increases by one step per scan cycle of the slow mirror.
As shown in fig. 3, normally the SLO fast (resonant) scan moves one step 12 in the orthogonal direction for every sine (or cosine) cycle 11 completed by the slow (linear) scan. Thus, the image frame rate (fps), the resonant frequency (f) of the fast scan mirror, and the number of lines (N) contained in each image frame (usually representing the maximum image height, and in particular the image width) satisfy the following relationship:
f＝fps·N
in the above formula, N includes all the scan lines 121 and 122 of fig. 3. Here, 121 is a rising ramp period of the sawtooth wave, and 122 is a return period.
The image of SLO generally does not include portion 122 of fig. 3 because there is a different pixel compression ratio for the image during 122 and the image during 121. The image of SLO is generally acquired only from section 121 of fig. 3.
The spectroscopic apparatus S1 shown in fig. 2 functions to transmit all incident light from the coupling device FC2, but to reflect all signals from the fundus to the APD. One mode of implementation is to dig a hollow cylinder at the axis of S1 to allow the incident focused light from FC2 to pass through, but reflect all the expanded light from the fundus to the photodetector APD, as shown in fig. 4, which is a schematic diagram of an implementation of the spectroscopy apparatus S1 shown in fig. 2.
As described above, the scan mirror M12 of FIG. 2 has two independent axes of motion. The first motion axis is orthogonal to the motion (scan) axis of M11 and the second motion axis is parallel to the motion (scan) axis of M11.
The orthogonal axes of motion of the motion (scan) axes of scan mirrors M12 and M11 receive two signals from the system mainframe: one is the sawtooth shown in fig. 3 (e.g., 121 and 122), and the other is a translation signal superimposed on the sawtooth. The sawtooth wave is used for scanning the fundus to obtain a fundus image, and the translation signal is used for optically tracking the eyeball motion of the fundus in the sawtooth wave scanning direction. As shown in fig. 5.
FIG. 5 is a schematic diagram of a manner of achieving fundus tracking in a sawtooth scanning direction with a sawtooth wave overlay offset.
As shown in fig. 5, when the target (e.g. eyeball) is at a reference time, i.e. the reference plane of the tracking algorithm, the scanning center of the sawtooth wave is at a relative zero position. When the eyeball starts to move relative to the reference surface, the control host adjusts the offset of the sawtooth wave in real time to track the position of the fundus relative to the reference surface.
The system control host may be a PC provided with a corresponding control program module, a device including a Field Programmable Gate Array (FPGA), a device including a Digital Signal Processor (DSP), a device using another type of electronic Signal Processor, or a combination device including these hardware.
For example: in the embodiment of the present invention, an Intel PC (Intel i7) is used to carry an nVidia image processor (GPU), such as GTX1050, for calculating eye movement signals (x, y, θ), then, through Xilinx FPGA (considering the cost factor, the embodiment of the present invention adopts the ML507 of Virtex-5 device or SP605 of Spartan 6; in the future, it is also possible to use the more powerful but more expensive FPGA devices of the latest series such as Virtex-6, Virtex-7, Kintex-7, Artix-7, etc. and also use the FPGA devices of other manufacturers such as Altera), by digitally synthesizing the y part of (x, y, theta) into the signal form of FIG. 5, and then sending it to a Digital-to-Analog Converter (DAC), such as DAC5672 from Texas Instruments, to control the first axis of motion of scanning mirror M12.
The signals in fig. 5 can also be realized by analog synthesis. In this case, the sawtooth of FIG. 5 generates a first analog signal from the first DAC. The offset of fig. 5, which is also the y component of (x, y, theta), is generated by the second DAC to produce a second analog signal. The two analog signals are combined by an analog signal mixer and finally sent to the first axis of motion of the scanning reflector M12.
The x of the signal (x, y, theta) is generated by another single DAC to be transmitted to the second motion axis of M12 for tracking the movement of the eyeball in the second motion axis. In the embodiment of the present invention, the second moving axis of the scanning mirror M12 is parallel to the scanning axis of the scanning mirror M11.
The translational part (x, y) of the eye movement signal (x, y, theta) has two orthogonal movement axes of M12 to realize closed loop optical tracking. The rotating part (θ) of the first imaging module 11 is implemented by digital tracking in the embodiment of the present invention, but may be implemented by optical or/and mechanical closed-loop tracking in the future. The related art of optical and/or mechanical tracking of the rotating part (θ) has been described in detail in US patent No. 9775515.
The embodiment of the utility model provides an in mentioned often switch two key terms: fundus tracking and eye tracking. In the related art of the present invention, fundus tracking and eyeball tracking are concepts. In clinical application, most of the physical movements come from the eyeball, and the movements of the eyeball cause random changes of the fundus images obtained by the imaging system along with time in space. An equivalent consequence is that at any one moment of the imaging system, different images are obtained from different fundus locations, the observed result being random dithering of the images over time. The embodiment of the utility model provides a tracking technology is in imaging system, catch eyeball motion signal (x, y, theta) through the ground of the eye in real time image, then feed back (x, y) to in the M12 of fig. 2, realize the scanning space locking of two scanning mirrors (M11 and M12 orthogonal in M11's direction) at any moment in a predefined ground of the eye physics space, thereby realize accurate ground of the eye tracking, stabilized the random variation of ground of the eye image along with time in space.
The imaging mode in fig. 2 (corresponding to the main module) constitutes a complete closed-loop control system for high-speed real-time tracking of fundus location. This part of the technology has been described in detail in two US patents US9406133 and US 9226656.
The imaging mode 2 of fig. 2, i.e., the left side "slave L2-M3-M2-S2-fundus" corresponds to the imaging mode 1 (master module) shown in fig. 1. One typical application is the use of Optical Coherence Tomography (OCT) imaging.
In fig. 2, "L31/L32-M2-S2-fundus" corresponds to the fundus laser treatment apparatus described in fig. 1. The functional implementation of OCT and fundus laser therapy is described in detail below.
M3 is a movable mirror. The movement may be mechanical or electronic, or a combination of both. The movable part of the mirror M3 may also be replaced by a beam splitting device.
In the embodiment of the present invention, the state of the mirror M3 is controlled mechanically. The state of M3 in/out of the optical system is determined by the state of coupling device FC1 of fig. 2. When light source L31/L32 is coupled into the optical system through FC1, M3 is pushed out of the optical system and the light of L31/L32 directly reaches mirror M2. When FC1 is not coupled into the optical system, M3 is placed in the position shown in fig. 2 to reflect light from L2 to mirror M2. The principle of mechanical control of the movable mirror M3 by FC1 is shown in fig. 6.
Fig. 6 is a schematic diagram illustrating a mechanism for controlling the mirror M3 according to an embodiment of the present invention.
As shown in fig. 6, in this mechanism, M3 is pushed out of or put into the optical system according to the insertion and extraction mechanism of FC 1. The switch is connected with a foldable mirror bracket through a connecting rod, when the switch is positioned at 90 degrees shown in the figure, the mirror bracket is opened, and meanwhile, an interface of the FC1 is also opened, so that the treatment laser can be accessed. As shown in fig. 6A. When the switch is closed, as shown in fig. 6B, at 0 degrees, the FC1 interface is closed, and the treatment laser is not accessible, and the foldable frame is returned to its original position (see fig. 2) to reflect imaging laser L2 into the system.
The mirror M3 functions to allow the user to select one of the functions of imaging mode 2 or fundus laser therapy in the slave module.
In realizing OCT imaging, that is, in the imaging mode 2 shown above, M3 is placed in the optical path of "L2-M3-M2-S2-fundus" shown in fig. 2, letting the light source of L2 reach the fundus.
In the case of imaging mode 2 shown in FIG. 2, light from L2 passes through M3 to M2. M2 is a two-dimensional scanning mirror, either a fast tilting mirror with a single reflective surface having two independent orthogonal control axes (e.g., S334.2SL from Physik instruments) or two one-dimensional tilting mirrors. The latter case is used in the present invention, employing the 6210H double mirror combination of Cambridge Technology, usa.
In the embodiment of the present invention, M2 in fig. 2 has multiple functions. In the case of imaging mode 2 shown in fig. 2, the system main unit generates an OCT scanning signal, controls the scanning mode of M2, and thereby controls L2 in the two-dimensional imaging space of the fundus.
In the embodiment of the present invention, the system host program generates a set of orthogonal scanning control base S as shown in fig. 7 by controlling the FPGAxAnd Sy. Where S isxAnd SyIs a vector of the tape direction.
Fig. 7 is a schematic diagram of a two-dimensional scanning mode for controlling the scanning spatial position of the OCT on the fundus according to an embodiment of the present invention.
The system host program multiplies the respective amplitudes (Ax and Ay) and signs by the two scanning bases of the FPGA (as shown in FIG. 7) to realize the two-dimensional scanning of the OCT in any direction of 360 degrees of the fundus and the designated field size, and the two-dimensional scanning can be expressed by the following relational expression:
OCT scan is SxAx+SyAy；
Wherein, the parameter AxAnd AyAlso vectors with signed (or) directions; sxAx+SyAyCan realize that the OCT can be scanned in any direction of 360-degree two-dimensional fundus space and in any field size allowed by an optical system。
Light from the light source L2 passes through the mirror M3, the scanning mirror M2, and the spectroscopic device S3 to reach the fundus. In the embodiment of the utility model provides an in, L2 is the imaging light source that the wavelength is 880nm, and light source L31 wavelength is 561nm, and light source L32 wavelength is 532 nm. Accordingly, the design of the light splitting device S3 needs to be changed differently for different auxiliary module light sources. One way is to customize a different splitter device S3 for different slave module light sources to be placed at the S3 position of fig. 2, as shown in fig. 8.
Fig. 8 is a schematic diagram of a design manner of a light splitting device S3 corresponding to the auxiliary module light source according to an embodiment of the present invention.
As shown in fig. 8, the light splitter S3 transmits 90% to 95%, reflects 5% to 10% of light at 532nm and 830nm or more, and transmits 5% to 10% of light at other wavelengths and reflects 90% to 95% of light at other wavelengths.
Referring to fig. 2, the light source L31 in the sub-module is an aiming light for laser treatment. The aiming light reaches the fundus, and the spot reflected from the fundus is received by the APD of the first imaging module 11, superimposing a spot generated by L31 on the SLO image. This spot position predicts that the therapeutic light L32 will have a nearly uniform spatial position at the fundus. The degree of overlap of the light sources L31 and L32 on the fundus depends on the lateral chromatism values (TCA) produced at the fundus by the two wavelengths 532nm and 561 nm.
In the embodiment of the utility model, the light with the wavelength of 532nm and 561nm does not exceed 10 microns in TCA generated at the eyeground. That is, after the 561nm aiming light of L31 was aligned with the fundus striking position, the 532nm therapeutic light misregistration position of L32 was not more than 10 μm.
The power of the aiming light of L31 to reach the fundus is typically below 100 microwatts, and the power of the treatment light of L32 to reach the fundus can be several hundred milliwatts or more. The signal amplitude of the L31 reflected from the fundus to the APD and the image signal amplitude of the SLO are close, but the high-power treatment light of 532nm still has a considerable signal reflected to the SLO through the spectroscopic device S3.
In order to prevent the treatment light from starting the fundus laser striking, 532nm signals returned from the fundus reach the SLO to impact the APD and cause overexposure of the APD, in the device of the embodiment of the present invention, a light splitting device S3 is placed in front of the APD. S3 reflects all light below 550nm and transmits all light above 550nm, thus playing a role in protecting APD.
The beam splitter S3 of FIG. 3 is movable in the opposite direction of M3. When the coupler FC1 is accessed to the optical system, S3 is also accessed to the optical system; when FC1 has not accessed the system, S3 is pushed out of the optical system. The optical system for accessing and pushing out S3 may be mechanical, electronic, or a combination of both. In the embodiment of the present invention, a mechanical method is adopted, and fig. 6 is referred to.
As described above, the auxiliary module integrates two functions, i.e., laser imaging, image stabilization, and laser treatment using the second imaging module 12 and the laser output adjustment module 13.
The switching between the two functions is realized by changing the position of M3. When M3 is placed in the optical system, the second imaging module 12 is activated and the laser therapy device is deactivated. When M3 is pushed out of the optical system, the laser treatment function is activated, while the second imaging module 12 is not operating.
The above is a description of an engineering implementation involving the second imaging module 12. The following describes an engineering implementation of the laser therapy function according to an embodiment of the present invention.
Referring to fig. 6, the positions of M3 and S3 in the optical system are controlled by the position of a knob mounted on the coupling device FC1, so as to realize the functions of dynamically switching the imaging mode 2 and the laser clinical treatment. Another function of the knob of FC1 is to connect and disconnect one or more electronic devices to alert the user and the system host control program which of two functions should be run.
Fig. 9 is a schematic diagram of a mechanical and electronic combined device for notifying a user and whether the current auxiliary module of the host control system is the imaging mode 2 or the laser therapy according to the embodiment of the present invention.
As shown in fig. 9, the device controls an LED indicator light through a conductive metal plate mounted on the knob of fiber coupler FC1 and provides high/low level signals to the electronic hardware to inform the user and the host control system whether the current slave module (slave module) is operating in imaging, image stabilization or laser therapy mode.
Under default setting, switch points A and B are disconnected, the LED is turned off, and a point C outputs 0V voltage or low level. The embodiment of the utility model provides an in, be used for detecting whether the input is low level (0V) or high level (3.3V or 2.5V) with the pin that C point is connected to FPGA to control mode automatic switch to formation of image, steady image mode or laser therapy mode.
When the FC1 knob is rotated 90 degrees (or some other angle, but in accordance with fig. 6), the conductive metal tabs turn on a and B, causing the LED to illuminate, while the potential at point C is pulled high. The control program can automatically switch the laser therapy function.
When set for imaging, image stabilization mode, the whole system can also be used only as imaging of imaging mode 1, such as SLO/SLO imaging only, without OCT. This mode of operation may be implemented by a system host control program.
In the imaging mode 1 in combination with the laser therapy mode of operation, the control M2 of fig. 2 incorporates a variety of laser shock modes including: 1) a single point percussion mode; 2) a regular spatial area array type striking mode; 3) and (4) self-defining a multipoint hitting mode in the irregular space area.
The single-point hitting mode is that a user determines a position to be hit by laser in a pathological area through a real-time image in the imaging mode 1, and starts therapeutic light after aiming at a target by aiming light, so as to hit the target according to preset parameters such as laser dose, exposure time and the like.
The regular spatial area array type striking mode is a scanning mode combining the single-point striking mode and the imaging mode 2, so that a user defines parameters such as laser dose and the like of each position, and then therapeutic light is started to strike a preset target one by one at equal time intervals.
The multi-point striking mode of the user-defined irregular space area is a complete free striking mode. The user self-defines parameters such as laser dose, exposure time and the like of any striking position in the striking pathological area, and then strikes the preset target one by one.
Preferably, in order to accurately control the amount of the laser beam reaching the target, in the embodiment of the present invention, a light splitting device is used to send a part of the light obtained from the therapeutic light L32 to a power meter. The value of the power detector is read in real time through a control program, and the laser dose reaching the striking target by the L32 power is dynamically adjusted to a preset value.
Preferably, in order to accurately control the exposure time of the laser to the target, the embodiment of the present invention uses the FPGA hardware clock to control the open and close states of L32. One way of control may be implemented by a real-time operating system, such as Linux. Another control mode can be realized by a non-real-time operating system such as Microsoft Windows installation real-time control software (Wind River); yet another way of control is by a timer on a completely non-real time operating system such as Microsoft Windows.
All functions of the auxiliary modules, imaging and image stabilization functions and laser treatment functions are supported by the real-time target (fundus) tracking and real-time image stabilization technology of the main module.
After the closed-loop fundus tracking function of the main module is started, the host control software displays the stable SLO/LSO images in real time. In the embodiment of the present invention, the spatial resolution of the image stabilization technique is about 1/2 of the lateral optical resolution of the imaging module 1. The stabilized real-time SLO/LSO images conveniently locate the spatial location of the fundus to be processed by the auxiliary module for the user.
The fundus tracking of the main module is a closed loop control system. After the fundus tracking function is activated, the master module (master module) controls the tracking mirror M12 to send the command to the slave module (slave module) M2 in a pre-calibrated mapping relationship. Thus, the light from L2 or L31/L32, after passing through M2 to the fundus, can be locked to a predetermined fundus position with considerable accuracy. One core technology is that the closed-loop control instruction of the main module is adopted to drive the open loop of the auxiliary module to track.
The spatial mapping relationship between M12 and M2, i.e. how to convert the control command (x, y, θ) of M12 into the control command (x ', y ', θ ') of M2, depends on the design of the optical system.
Here, the (x, y, θ) and (x ', y ', θ ') have the following relationship:
(x'，y'，θ')＝f(x'，y'，θ'；x，y，θ)(x，y，θ)
wherein (x ', y ', theta '; x, y, theta) can be achieved by calibration of the optical system.
The core technology is that the closed-loop control instruction of the main module (master module) drives the open-loop tracking of the slave module (slave module), and the closed-loop tracking is the optical tracking of the M12 closed loop and the M2 open loop.
Referring to fig. 7, again, the formula "OCT scan ═ SxAx+SyAy"as shown, the scanning mirror M2 of the sub module can perform optical scanning in any one direction of 360 ° in the two-dimensional space. The secondary module M2 is thus an open-loop optical tracking of the three variables (x ', y ', θ ') in the above equation, although the primary module has only a closed-loop optical tracking of translation (x, y) and a digital tracking of rotation θ.
The closed-loop tracking precision of the main module and the calibration precision of the above formula determine the open-loop tracking precision or target locking precision of the light from the auxiliary module reaching the eyeground. In the most advanced prior art, the closed loop optical tracking accuracy of the primary module is comparable to the optical resolution of the imaging system of the primary module, which is about 15 microns, and the open loop optical tracking accuracy of the secondary module can be 2/3-1/2, or 20-30 microns, of the closed loop optical tracking accuracy of the primary module. It is emphasized that these accuracies vary from system to system.
The utility model discloses mainly be applied to ophthalmology, the case to be diabetes retinal degeneration, old macular degeneration etc.. The utility model provides a solution is diagnose to the eye ground laser therapy technique, the automatic eye ground of support intelligence, also diagnose the service for a station form in the future and provide the material basis.
The above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention.
Claims (6)
1. An automatic switching device for an imaging mode and a treatment mode of a fundus laser treatment device, the automatic switching device comprising: a high-level conducting point A is arranged, a light emitting diode LED and a resistor which is connected in series by a resistor R1 and a resistor R2 are connected between the conducting point B and the working ground in parallel, and a conducting point C between the resistor R1 and the resistor R2 is connected to a chip pin of which the detection input end is high level or low level; the fundus laser treatment device is switched to a treatment mode or an imaging mode by controlling the conduction points A and B to be switched on or off.
2. The automatic switching device for the imaging mode and the treatment mode of the fundus laser treatment device according to claim 1, wherein the chip is a field programmable logic array FPGA.
3. The automatic imaging mode and treatment mode switching device of an eyeground laser treatment device as claimed in claim 1, wherein the circuit for controlling the conduction points a and B to be on or off is specifically: arranging a conductive metal sheet on the FC knob of the optical fiber coupler; rotating fiber coupler FC causes conducting point a to be on or off from conducting point B.
4. The automatic switching device for the imaging mode and the treatment mode of the fundus laser treatment device according to claim 1 or 3, wherein when the conductive points A and B are turned on, the LED is turned on, and the conductive point C is at a high level.
5. The automatic switching device for the imaging mode and the treatment mode of the fundus laser treatment apparatus according to claim 1 or 3, wherein the conducting point C outputs a low level when the conducting point a is disconnected from the conducting point B.
6. The automatic switching device for the imaging mode and the treatment mode of the fundus laser treatment device according to claim 1, wherein the imaging mode is confocal laser scanning imaging SLO or line scanning fundus camera LSO.
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