WO2020019169A1

WO2020019169A1 - Electrooculogram signal processing circuit and electrooculogram-based human-computer interaction system

Info

Publication number: WO2020019169A1
Application number: PCT/CN2018/096890
Authority: WO
Inventors: 王超; 李坤; 林国进
Original assignee: 高维度（深圳）生物信息智能应用有限公司
Priority date: 2018-07-24
Filing date: 2018-07-24
Publication date: 2020-01-30

Abstract

An electrooculogram signal processing circuit and an electrooculogram-based human-computer interaction system. The processing circuit comprises a differential electrode as well as a high-pass filter, a preamplifier (130), a trap filter, a single-end amplified low-pass filter, an ADC, and a master control unit that are in cascade connection with the differential electrode in sequence; the preamplifier (130) comprises an instrument amplifying unit, a threshold detecting and waveform shaping unit, and a gain control unit; the instrument amplifying unit is connected to the high-pass filter and the trap filter; the threshold detecting and waveform shaping unit is connected to the instrument amplifying unit; the master control unit is connected to the threshold detecting and waveform shaping unit, receives changed waveform, and outputs a corresponding first instruction to the gain control unit; the gain control unit receives the first instruction so as to set the gain of the instrument amplifying unit; and the master control unit receives an output signal from the ADC and outputs a corresponding second instruction. The electrooculogram signal collection flexibility can be fully improved, so that performance of collection of electrooculogram signals of a user in various scenarios is optimized.

Description

Ocular signal processing circuit and human-computer interaction system based on ophthalmology

Technical field

The invention relates to the field of biology-based human-computer interaction technology, and more particularly, to an electrooculogram signal processing circuit and an electrooculogram-based human-computer interaction system.

Background technique

In the current prior art, the ophthalmic signal acquisition circuit performs DC blocking on the signals collected by the electrodes, fixed gain amplification of the instrumentation amplifier, and then passes low-pass filtering, second-stage amplification, further low-pass filtering, AD conversion, and main processor, etc. deal with. For example, the ophthalmic signal acquisition circuit used in patent number CN 106775023 A and patent number CN 101598973A. The sensitivity of signal acquisition in these existing ophthalmic signal acquisition circuits is generally low. When the users are different, the same processing gain is used, because the power frequency carried by different users is different from 50Hz. In order to balance the 50Hz with strong interference, The users can also detect the accurate electrooculogram signal, which will inevitably reduce the sensitivity of the electroencephalogram signal detection for users with weak interference at 50Hz. Or when the same user is in different usage scenarios, for example, in a use environment where there are many electronic devices or 50Hz interference is strong, the sensitivity of the electrooculogram signal may decrease or even cause the electrooculogram signal acquisition due to excessive interference The circuit is saturated and cannot detect an accurate electrooculogram signal.

technical problem

The technical problem to be solved by the present invention is to provide an electrooculogram signal processing circuit and an electrooculogram-based human-computer interaction system in response to the above-mentioned low sensitivity defect in the prior art.

Technical solutions

The technical solution adopted by the present invention to solve its technical problem is to construct an ophthalmic signal processing circuit including a differential electrode, a high-pass filter, a pre-amplifier, a notch, and a single-end connected in cascade to the differential electrode. An amplifying low-pass filter, an ADC, and a main control unit; the pre-amplifier includes an instrument amplification unit, a threshold detection waveform shaping unit, and a gain control unit;

The instrument amplification unit is connected to the high-pass filter and the notch, and is configured to amplify an output signal of the high-pass filter and output the amplified signal to the notch;

The threshold detection waveform shaping unit is connected to the output end of the instrument amplification unit and the main control unit, and is configured to receive the output signal of the instrument amplification unit and perform waveform transformation, and send the changed waveform to the main control unit. ;

The main control unit is connected to the threshold detection waveform shaping unit, and is configured to receive the changed waveform and output a corresponding first instruction to the gain control unit;

The gain control unit is connected to the meter amplification unit, and is configured to receive the first instruction to set the gain of the meter amplification unit;

The main control unit is connected to the ADC, and is configured to receive an output signal of the ADC and output a corresponding second instruction.

Preferably, the differential electrode includes a horizontal differential electrode or a vertical differential electrode.

Preferably, the high-pass filter includes an RC high-pass filter with a cut-off frequency in the range of 2-4 Hz.

Preferably, the gain control unit includes at least one switch circuit and a resistor corresponding to the switch circuit, and the switch circuit is connected to the main control unit for receiving the first instruction to open or close, When the switch circuit is closed, its corresponding resistance is connected to the meter amplifying unit.

Preferably, the notch includes a 50 Hz notch with a 50 Hz frequency suppression greater than 50 dB.

Preferably, the cut-off frequency of the single-ended amplified low-pass filter is greater than or equal to 15 Hz.

The present invention also constructs a human-computer interaction system based on ophthalmology, which includes a spectacle frame and an ophthalmic signal processing circuit and a communication unit placed on the spectacle frame. The ophthalmic signal processing circuit is any of the above In the electrooculogram signal processing circuit, the communication unit is connected to a main control unit in the electrooculogram signal processing circuit, and is configured to send the second instruction to a controlled device that is communicatively connected to the communication unit.

Preferably, the electrooculogram signal processing circuit includes a first electrooculogram signal processing circuit and a second electrooculogram signal processing circuit, and the corresponding differential electrode in the first electrooculogram signal processing circuit is a horizontal differential electrode, and the second The corresponding differential electrode in the electrooculogram signal processing circuit is a vertical differential electrode.

Preferably, the human-computer interaction system further includes a ground electrode connected to the electrooculogram signal processing circuit.

Preferably, the human-computer interaction system further includes an acceleration sensor connected to the electrooculogram signal processing circuit and configured to detect interference caused by human motion.

Beneficial effect

The implementation of the electrooculogram signal processing circuit and the electrooculum-based human-computer interaction system of the present invention have the following beneficial effects: the sensitivity of collecting electrooculogram signals can be sufficiently improved, so that different persons or their electrocardiogram signals under different scenarios The acquisition performance is optimal.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention will be further described below with reference to the accompanying drawings and embodiments. In the drawings:

1 is a schematic structural diagram of an embodiment of an ophthalmic signal processing circuit according to the present invention;

2 is a circuit schematic diagram of an embodiment of an ophthalmic signal processing circuit according to the present invention;

3 is a schematic diagram of signal processing of an embodiment of an electrooculogram signal processing circuit according to the present invention;

FIG. 4 is a schematic structural diagram of an embodiment of a human-computer interaction system based on the electrooculogram of the present invention.

FIG. 5 is a schematic diagram of electrode placement in an embodiment of an electrooculogram-based human-computer interaction system according to the present invention; FIG.

FIG. 6 is a schematic diagram showing a comparison between the effects of the human-computer interaction system based on the electrooculogram of the present invention and the prior art.

Best Mode of the Invention

Type the description of the preferred embodiment of the invention here.

Embodiments of the invention

In order to have a clearer understanding of the technical features, objects, and effects of the present invention, specific embodiments of the present invention will now be described in detail with reference to the accompanying drawings.

As shown in FIG. 1, in the first embodiment of the electrooculogram signal processing circuit 100 of the present invention, it includes a differential electrode 110, a high-pass filter 120, a pre-amplifier 130, and a notch 140 connected in cascade to the differential electrode 110. , Single-ended amplifier low-pass filter 150, ADC160 and main control unit 170, the pre-amplifier 130 includes an instrument amplifier unit 131, a threshold detection waveform shaping unit 133, and a gain control unit 132; the instrument amplifier unit 131 is connected to the high-pass filter 120 and the trap The waver 140 is used to amplify the output signal of the high-pass filter 120 and output it to the notch 140; the threshold detection waveform shaping unit 133 is connected to the output of the meter amplification unit 131 and the main control unit 170, and is used to receive the meter amplification unit The output signal of 131 is subjected to waveform conversion, and the changed waveform is sent to the main control unit 170. The main control unit 170 is connected to the threshold detection waveform shaping unit 133, for receiving the changed waveform and outputting the corresponding first instruction to the gain control unit. 132; the gain control unit 132 is connected to the meter amplifying unit 131 for receiving a first instruction to set the gain of the meter amplifying unit 131; the main control unit 170 is connected The ADC 160 is configured to receive an output signal of the ADC 160 and output a corresponding second instruction. Specifically, the differential electrode 110 generally uses a non-polarized electrode, mainly an Ag-AgCl electrode, and collects weak ophthalmic signals through contact with the corresponding skin and conducts them to the subsequent circuit, such as the high-pass filter 120. After the ophthalmic signal is collected by the differential electrode 110, it is filtered by the high-pass filter 120 and the pre-amplifier 130 in order to amplify the filtered signal, and further filtered and amplified by the notch 140 and the single-ended amplified low-pass filter 150, and then sent. Perform analog-to-digital conversion to ADC160, and finally process the corresponding control signal output through the main control unit 170. Here, the control signal includes the main control unit 170 identifying and extracting the output signal of the ADC160 and converting it into a horizontal or vertical moving distance, or a click action. Wait for control signals. In some embodiments, the main control unit 170 uses STM32F107. Here the instrumentation amplifier unit 131 has ultra-low noise and high common-mode rejection ratio, and at the same time has a high gain (> = 500) and the gain is adjustable. Here, the device model used by the instrument amplification unit 131 may be INA333. Gain adjustment of the instrument amplification unit 131 is achieved by setting different external gain adjustment resistors RG. The user's human body carries a strong 50Hz power frequency signal, and a weak ophthalmic signal is superimposed on the 50Hz power frequency signal, and the strength of the power frequency signal interference varies with the environment of the person. When the power frequency signal is strong, it is amplified by the meter amplifying unit 131. If the gain of the meter amplifying unit 131 is too high, saturation will occur, which will cut off the amplitude of the power frequency signal superimposed with the ophthalmic signal and make the final output signal. Distortion causes the ophthalmic signal to be lost, which makes it impossible to extract the ophthalmic signal. Therefore, when the power frequency signal is strong, the gain of the meter amplifying unit 131 needs to be reduced to ensure that the output signal is not distorted, and the electrooculogram signal is not lost. The threshold value detection waveform shaping unit 133 converts 50 Hz power frequency signals of different amplitudes into pulse signals of different widths. The main control unit 170 counts pulse signals within a period of time according to a predetermined rule, and calculates a corresponding pulse width. Setting a plurality of different pulse width ranges corresponds to a plurality of different gains of the meter amplification unit 131 to ensure that the meter amplification unit 131 will not be saturated due to interference from a 50 Hz power frequency signal.

Referring to FIG. 3, input and output waveform diagrams of the threshold detection waveform shaping unit 133 in the pre-amplifier 130. The output of the meter amplifying unit 131 is the input of the threshold detection waveform shaping unit 133, which is a waveform in which the amplified electrooculogram signal is superimposed on a 50 Hz power frequency signal. The threshold detection waveform shaping unit 133 performs waveform shaping on a 50 Hz power frequency signal. Specifically, a hysteresis comparator can be formed by a comparator U5, and the comparator U5 can use MAX998. In the threshold setting of the hysteresis comparator:

High-level threshold: V + = R1 / R2 * VOH + (R1 + R2) / R2 * Vref

Low-level threshold: V-= (R1 + R2) / R2 * Vref

Among them, Vref is the DC offset output by the instrumentation amplifier unit 131, Vin is connected to the signal output terminal of the instrumentation amplifier unit 131, and the initial pulse width of the signal output by the instrumentation amplifier unit 131 is confirmed through the resistors R19 and R18. The input of the threshold detection waveform shaping unit 133 is a 50Hz sine wave or a sine-like wave. The above waveform is shaped by the threshold detection waveform shaping unit 133 to obtain a square wave signal. The input signal of the threshold detection waveform shaping unit 133 has a different amplitude and the output square wave signal is positive. The pulse width will be different. In this way, the gain of the meter amplifying unit 131 can be controlled according to the width of the positive pulse of the square wave signal. In the following table, as shown in FIG. 2, the square wave signal positive pulse width output by the threshold detection waveform shaping unit 133 is defined to correspond to two set values t1 and t2, and three of the meter amplification unit 131 corresponding to the set value Different gain settings. The main control unit 170 detects the corresponding relationship between the positive pulse width of the square wave signal output by the waveform shaping unit 133 and the set value according to the actual threshold value, and controls the gain control unit 132 to set the meter amplification unit 131 to the corresponding gain. It can be understood that 20ms is defined herein as the maximum value that can be output by the positive pulse width of the square wave signal output by the threshold detection waveform shaping unit 133. In some embodiments, it is not limited to 20ms.

Further, the differential electrode 110 includes horizontal differential electrodes 113 and 114 or vertical differential electrodes 111 and 112. Specifically, as shown in FIG. 5, according to the placement position of the differential electrode 110 used to collect the electrooculogram signal in the electrooculogram signal, which is also called a signal acquisition electrode, it can be defined as horizontal differential electrodes 113 and 114 and vertical differential electrodes 111 and 112. The two electrodes of the horizontal differential electrodes 113 and 114 are respectively placed near the corners of the eyes, and can be used to detect the corresponding electrooculogram signals generated by the movement of the eyeballs in the horizontal direction to generate control signals corresponding to the horizontal movements. The vertical differential electrodes 111 and 112 can be used to detect the corresponding electrooculogram signals generated by the vertical movement of the eyeball to generate a control signal corresponding to the vertical movement. Generally, the vertical differential electrodes can be set perpendicular to one eye, for example The right-eye vertical differential electrode, with the vertical center axis at the right-eye center line to the left, so that when the horizontal differential electrodes 113, 114 and the vertical differential electrodes 111, 112 are set together, the horizontal differential electrodes 113, 114 and the vertical differential electrode can be reduced as much as possible. 111 and 112 interfere with each other.

Further, as shown in FIG. 2, the high-pass filter 120 includes an RC high-pass filter with a cut-off frequency of -3dB in the range of 2-4Hz. Specifically, the high-pass filter 120 is generally constituted by an RC high-pass filter, and mainly blocks the direct current components of the differential electrodes 110. The cutoff frequency of RC high-pass filtering is usually designed at 2-4Hz. The cutoff frequency here should not be too small. Below 2Hz, it is easy to cause the signal baseline, that is, the signal horizontal line to be unstable. At the same time, the components C2 and R16, C8, and R17 in the RC high-pass filter 120 corresponding to the differential electrode 110 use high-precision components as much as possible to reduce the occurrence of common-mode to differential-mode signals to avoid interference with the electrooculogram signal.

Further, the gain control unit 132 includes at least one switch circuit and a resistor corresponding to the switch circuit. The switch circuit is connected to the main control unit 170 for receiving a first instruction to open or close. When the switch circuit is closed, The corresponding resistance is connected to the meter amplifying unit 131. Specifically, the gain control unit 132 is implemented by switching the gain control resistor through an analog switch. Analog switches can be single-pole multi-throw, multiple single-pole single-pole single-throw, or a combination of multiple single-pole double-throw, and are not limited to these modes. In Figure 2, the analog switches U4 and U7 can use TS3A4741. The number can be selected according to the level of gain control required. Here, three-level gain control is performed. Then select two TS3A4741 devices U4 and U7. The input of U4 and U7 is the same as the master. The GPIO interface of the control unit 170 is connected. Switching between U4 and U7 controls the selection terminal of the device by outputting different levels at different GPIO interfaces according to the gain set by the main control unit 170. The main control unit 170 performs pulse width detection on the output pulses of the threshold detection waveform shaping unit 133 and determines the pulse width interval. For details, refer to the table above to determine the corresponding gain of the meter amplification unit 131. Here, the main control unit 171 passes three The output levels of the GPIO interfaces gain_ctr1, gain_ctr2, and gain_ctr3. The three gain level control signals control the control terminals of the three analog switches. The three gain resistors R13, R14, and R15 are connected to the gain control pins of the instrumentation amplifier unit 131 through the analog switches U4 and U7. The gain resistors R13 and R14 , R15 can be preset according to the required gain. When the pulse width detected by the main control unit 170 is between 0 and t1 (including t1 here), the gain of the meter amplification unit 131 is A1, and the output levels of the three GPIO interfaces of the main control unit 170, gain_ctr1, gain_ctr2, and gain_ctr3 are 1, respectively. , 0 and 0 (can also be understood as 1 corresponding to high level, 0 corresponding to low level), the corresponding channel of the corresponding analog switch U4 is turned on, so that the gain resistor R13 instrumentation amplifier unit 131 gain control pin, control Gain of the meter amplifying unit 131.

Further, the notch filter 140 includes a 50 Hz notch filter 140 having a 50 Hz frequency suppression degree higher than 50 dB. Specifically, since the electrooculogram signal is superimposed on a very strong 50Hz industrial frequency signal, it is necessary to have extremely high suppression for the specific interference frequency, that is, the degree of suppression of the 50Hz industrial frequency signal at the frequency of the electrooculogram signal is at least 50dB or more. If a low-pass filter is used and two-stage active low-pass filtering is used, the low-pass cut-off frequency needs to be 10 Hz or lower. If a three-stage active low-pass filter is used, the low-pass cut-off frequency must be 18 Hz and lower. According to the experimental results, it can be known that the lower the cutoff frequency, the greater the impact on the ophthalmic signal attenuation or waveform distortion. Within 20Hz, it has a certain distortion effect on the waveform of the electrooculogram, especially the horizontal line. The 50Hz notch filter 140 with a 50Hz frequency rejection higher than 50dB is used to fully utilize its high Q characteristics to suppress a specific 50Hz power frequency signal, and the cutoff frequency can be set away from the frequency of the ophthalmic signal (5-10Hz) to prevent Distortion of the electrooculogram signal caused by filtering.

Further, the cut-off frequency of the single-ended amplified low-pass filter 150 is greater than or equal to 15 Hz. Specifically, the high-frequency interference is suppressed to a certain extent by the single-ended amplified low-pass filter 150 having a cutoff frequency greater than or equal to 15 Hz. At the same time, it has the amplification function, which can reduce the number of components, and also reduce the values of the filter elements R and C in the circuit, thereby improving the accuracy of the circuit and the consistency of the circuit.

In addition, as shown in FIG. 4, a human-machine interaction system based on the electrooculogram of the present invention includes a spectacle frame and an electrooculogram signal processing circuit 100 and a communication unit 200 placed on the eyeglass frame. The electrooculogram signal processing circuit 100 is In any of the above electro-optical signal processing circuits 100, the communication unit 200 is connected to the main control unit 170 in the electro-optical signal processing circuit 100, and is configured to send a second instruction to the controlled device 300 which is communicatively connected with the communication unit 200. Specifically, the glasses frame is provided with electrodes, and the signal acquisition electrodes are installed at the correct ophthalmic signal acquisition position, so as to achieve the best induction of weak ophthalmic signals. The collected electrooculogram signal is input to the electrooculogram signal processing circuit 100 through a shielded cable. The electrooculogram signal processing circuit 100 realizes amplification filtering of the weak electrooculogram signal and converts it into a digital signal, and the digital signal is transmitted to the digital signal by the main control unit 170. The signal is identified and extracted and converted into a control signal including a moving distance in a horizontal or vertical direction, or a click action. The control signal is sent through the communication unit 200 to the controlled device 300 communicably connected to the communication unit 200. The controlled device 300 receives the control The signal can be moved horizontally or vertically according to the control signal, or a corresponding click operation can be performed. For example, the actions of the human eye include basic actions such as left or right, up or down, and blinking. Through accurate recognition of these actions, it translates into the position and distance of the cursor movement in the controlled device 300, and analyzes actions such as blinking. It is a cursor click action, thereby achieving a relatively complete operation action or human-computer interaction behavior of the controlled device 300. Here, the connection between the communication unit 200 and the controlled device 300 may be wired or wireless, such as WIFI, Bluetooth, infrared, etc., or 3G, 4G, 4.5G, or even 5G communication methods. The controlled device 300 here includes a mobile terminal or device such as a mobile phone PC, a television, and of course, it is not limited to the above device.

Further, as shown in FIG. 5, the electrooculogram signal processing circuit 100 includes a first electrooculogram signal processing circuit 100 and a second electrooculogram signal processing circuit 100. The corresponding differential electrode 110 in the first electrooculogram signal processing circuit 100 is horizontal. The differential electrodes 113 and 114 and the corresponding differential electrodes 110 in the second electrooculogram signal processing circuit 100 are vertical differential electrodes 111 and 112. Specifically, as described above, in practical applications, horizontal differential electrodes 113 and 114 and vertical differential electrodes 111 and 112 corresponding to the position of the human eye may be set as required, and then pass through the horizontal differential electrodes 113 and 114 and the vertical differential electrode 111 as required. The ophthalmic signal processing circuits 100 corresponding to 112 and 112 respectively process different collected ophthalmic signals to achieve various control functions.

Further, the human-computer interaction system further includes a ground electrode 115 connected to the electrooculogram signal processing circuit 100. Specifically, the common ground of the ground electrode 115 and the ophthalmic signal processing circuit 100 can further reduce power frequency interference. The ground electrode 115 is usually placed at the center of the forehead or to the left. Of course, in some embodiments, it is not limited to the forehead, such as the earlobe, etc. All around the eyes. It is sufficient to maintain a proper distance from the relative position of the differential electrode 110.

Further, the human-computer interaction system further includes an acceleration sensor 400 connected to the electrooculogram signal processing circuit 100 and configured to detect interference caused by human motion. Specifically, the acceleration sensor 400 module detects the interference caused by the movement of the human body on the electrooculogram signal, so as to eliminate the interference of the human behavior of the user.

As shown in FIG. 6, the human-computer interaction system of the present invention and the hardware circuit design method in the prior art extract the ophthalmic signal. The signal A is an electrooculogram signal collected by the human-computer interaction system of the present invention, and the signal B is an electrooculogram signal collected by a method in the prior art. When the eyeball is rotated 2 degrees, the signal-to-noise ratio of signal A is SNRA = 20lg27 / 10 = 8.6dB, the signal-to-noise ratio of signal B is SNRB = 20lg27 / 17 = 4dB, and the signal-to-noise ratio of signal A is increased by 4.6dB, that is, the detection sensitivity The improvement is 4.6dB.

It can be understood that the above embodiments only express the preferred embodiments of the present invention, and their descriptions are more specific and detailed, but they should not be construed as a limitation on the scope of the patent of the present invention; it should be noted that for those of ordinary skill in the art In other words, without departing from the concept of the present invention, the above technical features can be freely combined, and several modifications and improvements can be made, all of which belong to the protection scope of the present invention; All equivalent transformations and modifications made shall fall within the scope of the claims of the present invention.

Claims

An ophthalmic signal processing circuit, comprising a differential electrode (110), a high-pass filter (120), a pre-amplifier (130), and a notch ( 140), a single-ended amplified low-pass filter (150), an ADC (160), and a main control unit (170), the pre-amplifier (130) includes an instrument amplification unit (131), and a threshold detection waveform shaping unit (133) And gain control unit (132);

The meter amplifying unit (131) is connected to the high-pass filter (120) and the notch (140), and is configured to amplify the output signal of the high-pass filter (120) and output to the notch.器 (140);

The threshold detection waveform shaping unit (133) is connected to the output end of the instrumentation amplification unit (131) and the main control unit (170), and is configured to receive an output signal of the instrumentation amplification unit (131) and perform waveform transformation. Send the changed waveform to the main control unit (170);

The main control unit (170) is connected to the threshold detection waveform shaping unit (133), and is configured to receive the changed waveform and output a corresponding first instruction to the gain control unit (132);

The gain control unit (132) is connected to the meter amplification unit (131), and is configured to receive the first instruction to set the gain of the meter amplification unit (131);

The main control unit (170) is connected to the ADC (160), and is configured to receive an output signal of the ADC (160) and output a corresponding second instruction.
The electro-optical signal processing circuit according to claim 1, wherein the differential electrode (110) comprises a horizontal differential electrode (113, 114) and a vertical differential electrode (111, 112).
The electro-optical signal processing circuit according to claim 1, wherein the high-pass filter (120) comprises an RC high-pass filter with a cut-off frequency in the range of 2-4 Hz.
The electrooculogram signal processing circuit according to claim 1, wherein the gain control unit (132) comprises at least one switch circuit and a resistor corresponding to the switch circuit, and the switch circuit and the main control unit A unit (170) is connected to receive the first instruction to open or close, and when the switch circuit is closed, its corresponding resistance is connected to the meter amplifying unit (131).
The electro-oculogram signal processing circuit according to claim 1, characterized in that the notch (140) comprises a 50 Hz notch with a 50 Hz frequency suppression degree higher than 50 dB.
The electro-oculogram signal processing circuit according to claim 1, wherein the cut-off frequency of the single-ended amplified low-pass filter (150) is greater than or equal to 15 Hz.

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A human-computer interaction system based on ophthalmic electricity, comprising an eyeglass frame and an ophthalmic signal processing circuit (100) and a communication unit (200) placed on the eyeglass frame, the ophthalmic signal processing circuit ( 100) The electrooculogram signal processing circuit according to any one of claims 1-6, the communication unit (200) is connected to a main control unit (170) in the electrooculogram signal processing circuit (100), and Sending the second instruction to a controlled device (300) that is communicatively connected with the communication unit (200).
The electro-optical human-computer interaction system according to claim 7, wherein the electro-optical signal processing circuit (100) comprises a first electro-optical signal processing circuit and a second electro-optic signal processing circuit, and the first The corresponding differential electrode in the one ophthalmic signal processing circuit is a horizontal differential electrode, and the corresponding differential electrode in the second ophthalmic signal processing circuit is a vertical differential electrode.
The human-computer interaction system based on the electrooculogram according to claim 8, characterized in that the human-computer interaction system further comprises a ground electrode (115) connected to the electrooculogram signal processing circuit (100).
The human-computer interaction system based on the electrooculogram according to claim 7, characterized in that the human-computer interaction system further comprises an electro-optical signal processing circuit (100) connected to detect the human body generated by human motion. Interfering acceleration sensor (400).

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