Medical springback tonometer excited by single coil

Abstract

The invention relates to a single-coil excited medical springback tonometer, which belongs to the technical field of medical instruments, is used for measuring intraocular pressure parameters of a patient and comprises a shell, a probe assembly, a forehead support assembly, a central processing unit and a display screen, the probe assembly comprises a probe, a probe base, a cartridge shell, two head coils and a tail coil; the head coil and the tail coil realize magnetization of the tail part of the probe, popping up the probe, pulling back the probe and collecting signals based on an electromagnetic induction principle; the probe pops up and rebounds after making contact with the eyeballs, the change of the speed of the probe causes the change of electric signals of the head coil and the tail coil, and electric signal parameters are converted into intraocular pressure parameters by detecting the change of the electric signals of the head coil and the tail coil and processing the signals. The problems that an existing tonometer needs to anesthetize a patient and is complex in operation are solved, operation is easy, measurement is faster, and cost is lower.

Description

Technical Field

[0001] The invention belongs to the technical field of medical devices, and in particular relates to a single-coil excited medical rebound tonometer. Background Art

[0002] With the aging population and the increasing popularity of electronic products, problems such as visual fatigue, visual impairment, and eye diseases are prevalent. Abnormal intraocular pressure or glaucoma is becoming younger and the incidence rate is increasing. At present, the number of people blinded by glaucoma in China has reached 6 million, but the early screening rate of glaucoma is low. The main reason is that the existing tonometers are not portable, the measurement accuracy is not high, and the patient's cooperation and the operator's proficiency are required.

[0003] There are various types of tonometers. In contact tonometers, a part of the measuring instrument (such as a probe) is in physical contact with the cornea to measure intraocular pressure, such as the Goldmann tonometer, the Schiόtz tonometer and the Pascal tonometer. The Goldmann tonometer measures intraocular pressure by flattening a corneal area with a diameter of 3.06 mm (patent US4260227, CN104799827A). The Schiόtz tonometer causes corneal depression by applying pressure to the cornea and converts the intraocular pressure by measuring the degree of corneal depression (US4192317, CN86204937U). For the above detection methods, they all require the cooperation of the patient and anesthesia of the patient, and have high requirements for measurement conditions and the proficiency of the operator. The Pascal dynamic contour tonometer uses a specially designed probe that adapts to the natural shape of the cornea and measures intraocular pressure by flattening a small part of the cornea. Although it has high accuracy, it is limited by its complexity and cost, and its application in clinical practice is relatively limited.

[0004] There are also non-contact tonometers (US Patents 5148807, 5279300 and 5299573, Japanese Patent JP2009-28287A), which measure intraocular pressure by ejecting a pulse of air to temporarily change the shape of the cornea. Although they are easy to use and provide high patient comfort, they cannot measure patients with irregular corneas, and the instruments are expensive and not portable.

[0005] The rebound tonometer is also a contact tonometer with the advantages of quick measurement, easy portability, and no need for anesthesia. It is based on the principle of electromagnetic induction, using the induction coil to magnetize part of the probe and pop out the probe. After the probe head hits the eyeball, it slows down and rebounds. By detecting the voltage change of the induction coil, the algorithm is used to convert the electrical signal parameters into intraocular pressure parameters. However, the existing rebound tonometer is relatively complex in design, and the segmented multi-section coil design of each induction coil also increases the complexity of the structure. Summary of the invention

[0006] Based on the technical problems existing in the prior art, the present invention provides a single-coil excited medical rebound tonometer, which has a simple structure and is easy to use. It is intended to solve the problems of the prior art solution that the patient needs to be anesthetized and the operation is complicated, and the operation is simple, the measurement is faster, and the cost is lower.

[0007] According to the technical solution of the present invention, the present invention provides a single-coil excited medical rebound tonometer, which includes a shell, a probe assembly, a central signal processing unit and an interactive display unit, wherein the shell is used to provide body protection and support for the single-coil excited medical rebound tonometer; the probe assembly is used to pop out the probe and the probe contacts the measurement target, and with the help of the opposite action of the measurement target, the rear part of the probe rebounds into the measurement cavity of the tonometer; the central signal processing unit is used to collect and process signals, and to detect, receive and process voltage changes on the single excitation coil to calculate the intraocular pressure of the measurement target; the interactive display unit is used to display the working status of the single-coil excited medical rebound tonometer and the intraocular pressure data calculated by the central processing unit, and receive external input control signals.

[0008] The single excitation coil is a head coil or a tail coil. The single coil excitation medical rebound tonometer further comprises a forehead support assembly and an energy supply unit; the forehead support assembly is used to support or lean against the support body to adjust the distance between the front of the probe and the target to be measured; the forehead support assembly further comprises a dial, and the rotating dial pushes the forehead support assembly forward and backward through the spiral support; the energy supply unit provides power for rotating the dial and electricity for the excitation assembly.

[0009] Furthermore, the probe assembly includes a probe, a probe base, a cartridge case, a head coil and a tail coil; one of the head coil or the tail coil realizes magnetization of the tail part of the probe and collects signals based on the principle of electromagnetic induction, and the other coil pops out the probe and pulls back the probe.

[0010] Preferably, the probe pops out and rebounds after contacting the eyeball, and the change in the probe speed causes the change in the electrical signals of the head coil and the tail coil. The electrical signal parameters are converted into intraocular pressure parameters by detecting the changes in the electrical signals of the head coil and the tail coil and processing the signals.

[0011] More preferably, in a single-coil excited medical rebound tonometer, only one coil is used at the same time to realize the magnetization of the probe and the measurement of the electrical signal parameters. When the probe is loaded into the device, the probe is in a non-magnetized state; when the energy supply unit is turned on and the probe is excited by the single excitation coil, the probe is magnetized. When the energy supply unit is turned on and the probe is magnetized by the excitation coil, the magnetic material at the tail of the probe is magnetized by the energized excitation coil.

[0012] Preferably, after pressing the measurement button, the head coil or the tail coil is powered off and the magnetization excitation is terminated, a forward excitation signal is applied to the head coil, the probe is energized by the head coil to form a magnetic field that attracts it and impacts the eyeball, the probe is ejected and contacts the eyeball, and then rebounds.

[0013] Compared with the prior art, the single-coil excited medical rebound tonometer of the present invention has the following beneficial technical effects: 1. The present invention is a rebound tonometer, which does not require anesthesia of the patient, is more convenient to measure and has lower cost; 2. Compared with the prior art, the present invention reduces the complexity and cost of the system; 3. Compared with the prior art, the irregular shape of the cornea does not affect the measurement, does not require precise optical instrument focusing, has a wider range of applications, lower costs, and lower system complexity; 4. The rebound pressure gauge of the present invention is a portable device with simple operation and high safety; 5. The present invention integrates the magnetization and signal acquisition functions of the probe into one coil, which reduces the complexity and cost of the system and solves the vibration problem of the probe head when using two coils. BRIEF DESCRIPTION OF THE DRAWINGS

[0014] Figure 1 The figure is a general view of a single-coil excited medical rebound tonometer according to an embodiment of the present invention.

[0015] Figure 2 yes Figure 1 A perspective view of a single-coil excited medical rebound tonometer rotated 90 degrees is shown.

[0016] Figure 3 is a schematic view of a probe assembly according to an embodiment of the present invention.

[0017] Figure 4 The figure is a schematic diagram of the measurement process of a medical rebound tonometer according to an embodiment of the present invention.

[0018] Figure 5 is a schematic diagram of functional modules according to an embodiment of the present invention.

[0019] Figure 6 Schematic diagram of a reverse protection circuit of an energy supply unit according to an embodiment of the present invention.

[0020] Figure 7 It is a schematic diagram of an adapter power supply / USB communication circuit according to an embodiment of the present invention.

[0021] Figure 8 Schematic diagram of a power detection circuit of an energy supply unit according to an embodiment of the present invention.

[0022] Fig. 9 2 is a schematic diagram of a charging circuit of an energy supply unit according to an embodiment of the present invention.

[0023] Fig.10 FIG. 4 is a schematic diagram of a key detection circuit according to an embodiment of the present invention.

[0024] Fig.11 FIG. 4 is a schematic diagram of a key detection circuit according to an embodiment of the present invention.

[0025] Fig.12 FIG. 4 is a schematic diagram of a key detection circuit according to another embodiment of the present invention.

[0026] Fig.13 Schematic diagram of a DC / DC buck circuit according to an embodiment of the present invention.

[0027] Fig.14 Schematic diagram of a DC / DC boost circuit according to an embodiment of the present invention.

[0028] Fig.15 Schematic diagram of a probe coil connection interface according to an embodiment of the present invention.

[0029] Fig.16 is a schematic diagram of an L1 coil control circuit according to an embodiment of the present invention.

[0030] Fig.17 is a schematic diagram of an L2 coil control circuit according to an embodiment of the present invention.

[0031] Fig.18 FIG. 4 is a schematic diagram of an intraocular pressure sampling circuit according to an embodiment of the present invention.

[0032] Fig.19 is a schematic diagram of a timer circuit according to an embodiment of the present invention.

[0033] Fig. 20 It is a schematic diagram of a Bluetooth and buzzer connection interface according to an embodiment of the present invention.

[0034] Fig.21 FIG. 4 is a schematic diagram of an LCD connection interface according to an embodiment of the present invention.

[0035] Fig. 22 is a schematic diagram of a data storage circuit according to an embodiment of the present invention.

[0036] Fig.23 Schematic diagram of a main control MCU according to an embodiment of the present invention.

[0037] Description of reference numerals in the accompanying drawings: 1. Outer shell; 2. Soft rubber head for supporting forehead; 3. Dial for adjusting the distance between instrument and eyes; 4. Probe assembly; 5. Interactive display unit; 6. Energy supply unit; 7. Central signal processing unit; 8. Charging slot; 9. Power key; 10. Measurement key; 11. Narrow part; 12. Data transmission port; 13. Probe head; 14. Probe base; 15. Cylinder shell; 16. Head coil; 17. Probe tail; 18. Tail coil. DETAILED DESCRIPTION

[0038] In order to make the purpose, technical solution and advantages of the present invention clearer, the technical solution of the present invention will be clearly and completely described below in conjunction with the drawings in the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0039] It should also be noted that, for ease of description, only the parts related to the invention are shown in the drawings. In the absence of conflict, the embodiments of the present invention and the features in the embodiments can be combined with each other.

[0040] It should be noted that the concepts such as "first" and "second" mentioned in the present invention are only used to distinguish different devices, modules or units, and are not used to limit the order or interdependence of the functions performed by these devices, modules or units.

[0041] It should be noted that the modifications of "one" and "plurality" mentioned in the present invention are illustrative rather than restrictive, and those skilled in the art should understand that, unless otherwise clearly indicated in the context, it should be understood as "one or more".

[0042] The present invention belongs to the field of medical devices. The present invention is a single-coil excited medical rebound tonometer, which is mainly used for measuring intraocular pressure parameters of patients. The medical rebound tonometer mainly includes a housing, a probe assembly, a forehead support assembly, a central processing unit for collecting signals and processing signals, and a display screen. The key component for realizing intraocular pressure measurement in the present invention is the probe assembly. The probe assembly includes a probe, a probe base, a cartridge case, a head coil and a tail coil. The head coil and the tail coil realize the magnetization of the tail part of the probe, the ejection of the probe, the retraction of the probe and the acquisition of signals based on the principle of electromagnetic induction. After the probe is ejected and contacts the eyeball, it rebounds. The change in the probe speed causes the change in the electrical signal of the head coil and the tail coil. The electrical signal parameters are converted into intraocular pressure parameters by detecting the change in the electrical signal of the head coil and the tail coil and signal processing. The present invention solves the problem that the existing technical solution requires anesthesia of the patient and the operation is complicated, and the operation is simple, the measurement is faster, and the cost is lower.

[0043] See also Figure 1 and Figure 2 , Figure 1 A practical embodiment of the device according to the invention is described, and Figure 2 Its cross section is shown. A single-coil excited medical rebound tonometer according to one embodiment of the present invention comprises a housing 1, a probe assembly 4, a central signal processing unit 7, an interactive display unit 5, a forehead rest assembly, an energy supply unit 6 and a switch. The housing 1 is used to provide body protection and support for the single-coil excited medical rebound tonometer. The housing 1 is elongated at the bottom and comprises a forehead rest assembly and a probe assembly 4 at the upper end. The forehead rest assembly is used to support or abut against a support body to adjust the distance between the front of the probe and the target to be measured; the forehead rest assembly further comprises a dial wheel 3, and the rotating dial wheel 3 pushes the forehead rest assembly forward and backward through a spiral support. In another embodiment, the forehead rest assembly comprises a soft rubber head 2 for supporting the forehead, and a dial wheel 3 for adjusting the distance between the instrument and the eye. In one embodiment, the dial wheel 3 for adjusting the distance between the single-coil excited medical rebound tonometer and the eye can be rotated to adjust the distance between the single-coil excited medical rebound tonometer and the eye, that is, the single-coil excited medical rebound tonometer is properly pressed against the patient's forehead by the extended length of the soft rubber head 2 of the forehead support assembly supporting the forehead, thereby making the probe assembly 4 at a suitable distance from the patient's eye.

[0044] The probe assembly 4 comprises a probe head 13 and a probe tail 17 for contacting the patient's eye for detection, a probe base 14 for fixing the probe, a cartridge case 15 for accommodating the probe base, and a head coil 16 and a tail coil 18 wound on the cartridge case. Different from the prior art, the probe in the present invention is fixed or accommodated in the probe base 14, the probe base is sleeved in the cartridge case, and the coil (head coil and tail coil) for exciting the probe is wound on the cartridge case. Such a design enables the probe to always remain at the position of the central axis during the entire launch or ejection process, and thus the magnetization effect it receives is very uniform and controllable; and during the ejection process of the probe, the probe is facing the patient's eye to ensure the angle at which the probe contacts the patient's eye, thereby avoiding the problem of large measurement errors caused by different measurement angles in different measurement processes in the prior art tonometer during repeated measurements.

[0045] In a preferred embodiment, the probe head is made of plastic, and the probe tail is made of a magnetic material, preferably steel; the probe tail 17 and the probe head 13 can be separated, so that the probe head 13 can be disposable. The probe base 14 for fixing the probe and the cartridge case 15 for accommodating the probe base are preferably made of non-magnetic materials, such as plastic, and the probe head 13 and the probe tail 17 are installed in the probe base 14 and the cartridge case 15 for accommodating the probe base, and the probe tail 17 moves in the cartridge case.

[0046] The present invention further includes an interactive display unit 5 and an energy supply unit 6 and a switch key, wherein the interactive display unit 5 is used to display the measurement results and adjustment parameters, and further, the interactive display unit 5 is used to display the working state of the single-coil excited medical rebound tonometer and the intraocular pressure data calculated by the central processing unit 7, and receive external input control signals and control parameters. The energy supply unit 6 provides energy support for the device, and further, the energy supply unit 6 provides power for rotating the dial and power for the excitation component. The single-coil excited medical rebound tonometer of the present invention is also equipped with a charging slot 8 and a data transmission port 12. Preferably, the charging slot 8 and the data transmission port 12 are arranged at the lower part of the grip, and more preferably arranged on the bottom end surface of the grip, and an external charger or power supply can be connected to the charging slot to charge the energy supply unit; in one embodiment, the energy supply unit is a rechargeable DC battery; in another embodiment, the energy supply unit can be any type of existing DC power supply or dry battery.

[0047] The data transmission port is used to transmit the measurement data to an external device and perform big data analysis; further, the calibration data is transmitted to the central signal processing unit 7 through the data transmission port, so as to adjust the precision and accuracy of the measurement data in real time. In the present invention, transmitting the calibration data to the central signal processing unit through the data transmission port is one of the innovative points that distinguish the single-coil excited medical rebound tonometer of the present invention from the existing tonometers. The precision and accuracy of the measurement data are ensured by real-time calibration. At the same time, the historical data of a patient can be transmitted to the central signal processing unit through the data transmission port. Then, on the single-coil excited medical rebound tonometer of the present invention, the historical data of a patient can be compared and analyzed with the real-time data without leaving the machine or going offline, which can promote the popularization of the single-coil excited medical rebound tonometer for home use.

[0048] In one embodiment, a narrow portion 11 is provided on the upper part of the grip portion. The narrow portion 11 is a thinner portion for holding relative to the grip portion body, and is located at the part surrounded by the thumb and index finger when the hand is held. The design of the narrow portion 11 conforms to human mechanics, so that the single-coil excited medical rebound tonometer is comfortable to use and not easy to fall off; it is more suitable for patients to measure or test themselves at home.

[0049] The switch key 9 is used to switch the device on and off, and the measurement key 10 is used to start measurement. In the embodiment, when the switch key 9 of the single-coil excited medical rebound tonometer is pressed, the single-coil excited medical rebound tonometer is started to energize the coil, and the dial wheel 3 of the distance between the single-coil excited medical rebound tonometer and the eye is appropriately adjusted, so that the dial wheel 3 rotates to adjust the distance between the single-coil excited medical rebound tonometer and the eye, and after reaching a suitable support position and measurement position, the measurement key 10 is pressed, and the single-coil excited medical rebound tonometer immediately launches a probe toward the eye and starts measurement.

[0050] The present invention further comprises a central signal processing unit 7, which is used to detect, receive and process changes in electrical signals on the head coil and the tail coil, preferably changes in voltage signals, to calculate the intraocular pressure of the measurement target.

[0051] like Figure 3 The probe head 13 and the probe tail 17 shown are assembled into a complete set of probes, the probe is fixed in the probe base 14 and the probe base is contained in the cartridge case 15, the solenoid type head coil 16 and tail coil 18 are surrounded by the probe, wherein the tail coil is used to magnetize the magnetic material of the probe tail, and the head coil is used to provide the probe with a specific speed to hit the eye and orient accordingly when measuring the intraocular pressure of the eye. In one embodiment, the head coil and the tail coil realize the magnetization of the tail part of the probe (17), ejection of the probe, retraction of the probe and signal collection based on the principle of electromagnetic induction; the probe is ejected and rebounds after contacting the eyeball, and the change of the probe speed causes the change of the electrical signal of the head coil and the tail coil, and the electrical signal parameters are converted into intraocular pressure parameters by detecting the change of the electrical signal of the head coil and the tail coil and signal processing. In another embodiment, only one coil is used at the same time to realize the magnetization of the probe and the measurement of the electrical signal parameters. In a preferred embodiment, the head coil and the tail coil are used to alternately magnetize the probe and measure the electrical signal parameters at the same time. In another embodiment, when the probe is loaded into the device, the probe is in a non-magnetized state; when the energy supply unit is turned on and the probe is excited by the tail coil, the probe is magnetized. Alternatively, when the energy supply unit is turned on and the probe is excited by the tail coil, the magnetic material at the tail of the probe is magnetized by the energized tail coil. Alternatively, when the probe is loaded into the device, the probe is in a non-magnetized state; when the energy supply unit is turned on and the probe is excited by the head coil, the probe is magnetized. When the energy supply unit is turned on and the probe is excited by the head coil, the magnetic material at the tail of the probe is magnetized by the energized head coil.

[0052] In another embodiment, after the measurement key is pressed, the head coil or the tail coil is powered off and the magnetization excitation is terminated, an excitation signal is applied to the head coil in the forward direction, the probe is energized by the head coil to form a magnetic field and the probe impacts the eyeball, the probe is ejected and contacts the eyeball, and then the probe rebounds. In another embodiment, after the measurement key is pressed, the head coil or the tail coil is powered off and the magnetization excitation is terminated, an excitation signal is applied to the head coil in the forward direction, the probe is energized by the head coil to form a magnetic field and the probe impacts the eyeball, the probe is ejected and contacts the eyeball, and then the probe rebounds. Corresponding to the above embodiment, and optionally, after the probe rebounds, the tail coil is stimulated to retract the probe. In another embodiment, the tail coil detects changes in electrical signals, and the electrical signals are collected and processed by the intraocular pressure measurement circuit. In another embodiment, the tail coil detects changes in voltage, and the voltage is collected and processed by the intraocular pressure measurement circuit.

[0053] In one embodiment, when the probe is installed in a medical rebound tonometer with single coil excitation, the magnetic material at the tail of the probe is magnetized by the energized head coil or tail coil to form an N / S pole; and with the change of the polarity of the head coil or tail coil, the magnetic material at the tail of the probe is repeatedly magnetized, thereby achieving the magnetic enhancement of the magnetic material at the tail of the probe. In another embodiment, the head coil is not energized, or the two head coils and tail coils can be quickly switched to be energized, and the magnetization intensity of the tail of the probe is enhanced through the joint action of a single tail coil or the head coil and the tail coil, that is, only one head coil is used at the same time or the probe is partially magnetized. After the measurement is completed, the probe rebounds after contacting the eyeball, the head coil is energized to form a retraction magnetic field to pull back the probe, and the probe is ejected; at the same time, the tail coil performs the measurement action. Conversely, in another embodiment, after the measurement is completed, the probe rebounds after contacting the eyeball, the tail coil is energized to form a retraction magnetic field to pull back the probe, and the probe is ejected; at the same time, the head coil performs the measurement action. During this measurement process, the intraocular pressure value is calculated through an algorithm based on the changes in different electrical signals caused by the different speeds of the probe's retreat.

[0054] According to the second aspect of the technical solution of the present invention, the use of only one coil to realize the magnetization of the probe is taken as an example to illustrate the smooth measurement of the medical rebound tonometer of the present invention.

[0055] like Figure 4 As shown in the figure, the medical rebound tonometer measurement process includes the following steps: Step S1: power on; insert the probe, press the power button, start the medical rebound tonometer, and power on; Step S2: magnetizing the probe; sucking the probe back to the designated position, that is, making the probe reach the designated position, starting the tail coil to begin magnetizing the probe tail, and magnetizing the probe through the tail coil (L2) for 500ms, so that the probe tail is magnetized; in another embodiment, by changing the current direction of the tail coil, the magnetic field generated by the tail coil continuously changes direction, so that the probe tail is continuously excited or magnetized in the changing magnetic field, thereby obtaining a probe tail with enhanced magnetization.

[0056] Step S3: launching the electromagnetically excited probe to measure the intraocular pressure; energizing the head coil (L1), pressing the measurement key to start the measurement, the head coil drives the probe to pop out toward the patient's eye, and the probe hits the cornea and rebounds; after detecting the probe rebounding, the head coil pulls the probe back to a specified position; at the same time, the tail coil 18 measures the electrical signal caused by the rebounding probe; Step S4: Collect data from the rebounded probe; determine whether the collected data is valid. If it is too close or too far, it will prompt a data error and return and re-measure. That is, if it is too close or too far, it will return from step S4 to step S2 and start measuring again; the peak voltage collected by the intraocular pressure measurement circuit for the rebounded probe is V OUT The signal acquisition time period during measurement is within 40ms; if the voltage signal is not collected within 40ms, a command will be issued to let the tail coil suck back (pull back) the probe, and it will be judged that the distance between the probe head and the eye is too far during the initial measurement; the peak voltage of the collected voltage signal should be ≥3V, such as the voltage V collected within 40ms OUT If the value is less than 3V, the electrical signal data is considered invalid, and it is judged that the distance between the probe head and the eye is too close during the initial measurement; Step S5: The tail coil (L2) sucks back the probe and performs data processing, monitors the electrical signal of the tail coil, obtains the intraocular pressure value through electrical signal processing, and the interactive display unit displays the intraocular pressure value result.

[0057] In the measurement process of the medical rebound tonometer, the arrangement of the coils of the present invention and the direction of applying the electric field can be implemented in different ways to achieve the required moving direction of the probe. In the present invention, the position, distance, number and size of the coils (head coil and tail coil) relative to the position of the probe base 14 for fixing the probe and the cartridge case 15 for accommodating the probe base, and the length of the probe can be varied in various ways.

[0058] In one embodiment, only one coil is used at the same time to realize the magnetization of the probe and the measurement of the electrical signal parameters, which can be a head coil or a tail coil. The present invention can also integrate the magnetization and signal acquisition functions of the probe into one coil, thereby reducing the complexity and cost of the system. In another embodiment, the magnetization enhancement or strengthening of the tail of the probe can be realized by a single coil, thereby solving the problem of the tremor of the probe head caused by the simultaneous magnetization of the tail of the probe using two coils; and after solving the tremor of the probe, the degree of wear or damage of the probe to the probe base and the cartridge case is greatly reduced, thereby greatly improving the service life of the single-coil excited medical rebound tonometer.

[0059] Furthermore, the present invention provides a single-coil excited medical rebound tonometer control circuit system, the single-coil excited medical rebound tonometer control circuit system includes a charging and energy supply unit power detection circuit, a key function circuit and a measurement circuit, such as Figure 5-Figure 8 As shown, Figure 5 The functional modules of a single-coil excited medical rebound tonometer control circuit system are shown; Figure 6 The reverse protection circuit of the energy supply unit is shown; Figure 7 Shows the adapter power supply / USB communication circuit; Figure 8 The energy supply unit power detection circuit is shown.

[0060] The Type-C charger, the Type-C adapter board PCA, the energy supply unit management IC, and the energy supply unit constitute a charging and energy supply unit power detection circuit; the charging and energy supply unit power detection circuit is used to charge the energy supply unit and detect the power of the energy supply unit. The energy supply unit is preferably a lithium energy supply unit (for example, a lithium battery); the Type-C charger is used to charge the energy supply unit. In one embodiment, the Type-C charger can provide 5V / 1A power supply. In the present invention, the Type-C charger is configured with an energy supply unit reverse protection circuit to protect the energy supply unit from damage to the internal components of the energy supply unit due to reverse connection.

[0061] The Type-C adapter board PCA is used to realize the connection between the Type-C charger and the main control board; the Type-C adapter board PCA constitutes an adapter power supply / USB communication circuit, and only performs charging operations when the adapter is powered; when connected to a computer, the Type-C adapter board PCA will realize two-way communication with the computer (the same as uploading pictures or upgrading programs). In one embodiment, the Type-C adapter board PCA is connected to the battery management IC. Furthermore, the output end of the Type-C charger is connected to the input end of the Type-C adapter board PCA, and the output end of the Type-C adapter board PCA is connected to the input end of the energy supply unit management IC, and the input end of the energy supply unit is connected to the energy supply unit management IC, and the energy supply unit supplies power to the entire system. The energy supply unit is preferably a lithium battery. The battery management IC connects to the lithium battery and manages the lithium battery.

[0062] The energy supply unit (for example, a lithium battery) is used to power the entire single-coil excited medical rebound tonometer; the energy supply unit constitutes an energy supply unit charging circuit, charges the energy supply unit, and indicates the charging status (charging, fully charged) and displays it on the display screen of the interactive display unit.

[0063] The energy supply unit management IC is used to detect the power level of the energy supply unit, limit and detect the charging current, and indicate the charging status; the energy supply unit management IC constitutes the energy supply unit power detection circuit, and the sampled voltage will also increase or decrease as the power level of the energy supply unit increases or decreases, and power detection is performed on this. In a preferred embodiment, the energy supply unit management IC includes a perpetual calendar, a FLASH chip, an intraocular pressure measurement circuit, an MCU, and a battery management IC. The input end of the perpetual calendar is connected to the output end of the MCU, the input end of the FLASH chip is connected to the output end of the MCU, and the input end of the intraocular pressure measurement circuit is connected to the output end of the MCU. The perpetual calendar is used to realize the time setting of year, month, day, etc., and the FLASH chip is used to store the collected data, interface images, etc. The intraocular pressure measurement circuit is used to collect intraocular pressure data and calculate the obtained data through an algorithm to obtain the value of intraocular pressure; the MCU (central control unit) collects signals and controls related functional modules, such as key functions, display functions, etc. In a preferred embodiment, the perpetual calendar communicates with the MCU through an IC, and the MCU is preferably CH32F103R8T6.

[0064] The energy supply unit management IC further includes a Bluetooth adapter board PCA, a 1.3-inch display screen, a keypad PCA, and an LCD adapter board PCA, which are used to control the ejection and retraction (pulling back) of the probe, and to drive the two coils, the head coil and the tail coil, respectively, by controlling the MOS tube and the triode connected between the head coil and the tail coil, and to collect, calculate, and detect the probe rebound signal. The input end of the Bluetooth adapter board PCA is connected to the output end of the MCU, the input end of the LCD adapter board PCA is connected to the output end of the MCU, and the output end of the LCD adapter board PCA is connected to the input end of the 1.3-inch display screen. The Bluetooth adapter board PCA is used to implement the Bluetooth function, interact with the MCU to collect, control, and send data, and there is also a buzzer control circuit on the board, which can set the volume and switch of the prompt sound and alarm sound; the 1.3-inch display screen is used to display measurement data, error reporting, date and time, etc.; the LCD adapter board PCA is used to realize the connection between the 1.3-inch display screen and the main control board.

[0065] like Figure 6 As shown, a battery reverse protection circuit is shown to protect the internal components of the energy supply unit management IC from damage caused by reverse connection of the battery; the J3 connector (preferably 1.25MM-4P) is connected to the lithium battery to power or charge the circuit board; the power signal terminal U3_BAT is connected to the battery terminal on the battery management chip to charge the battery; the signal VUSB is the signal on the adapter power supply / USB communication circuit, and after passing through the Schottky diode RB491D, the signal BAT powers the subsequent circuit. The ferrite bead FB5 (preferably HCB1608KF-200T30) filters out the high-frequency noise and spike interference on the power line, and the field effect tube Q1 is used for isolation between the power supply U3_BAT and the BAT signal, as well as the anti-reverse connection function.

[0066] In one embodiment, the input end of the ‌J3 connector is connected to the output end of the lithium battery, the output end of the ‌J3 connector is connected to the input end of the ferrite bead FB5, the output end of the ferrite bead FB5 is connected to the input end of the field effect tube Q1, the output end of the ferrite bead FB5 is connected to the input end of the capacitor C11 (preferably 0.1uF / 50V), the output end of the field effect tube Q1 is connected to the input end of the resistor R21 (preferably 10K ohms), the input end of the field effect tube Q1 is connected to the output end of BAT, a Schottky diode D1 is connected in series between VUSB and BAT, and a Schottky diode D2 is connected in series between VUSB and the resistor R21.

[0067] In another embodiment, the connector J3 is connected to a lithium battery, and the positive electrode of the lithium battery is connected to the drain of the MOS tube Q1 through the magnetic bead FB5; the power signal VUSB (provided by the connector J5, which is the input power of the USB) is connected to the source of the MOS tube Q1 through the Schottky diode D1 and the signal is defined as BAT; the power signal VUSB is connected to GND through the diode D2 and the resistor R21, and the cathode of the diode is connected to the gate of the MOS tube Q1; when the USB power supply is connected to the circuit board, the power signal VUSB provides a voltage of VUSB-0.45V to the source of the MOS tube Q1 through the Schottky diode D1, and the power signal VUSB provides a voltage of VUSB-1.2V to the gate of the MOS tube Q1 through the diode D2; the voltage Vgs between the gate and source of the MOS tube Q1 is less than -0.7V, and the MOS tube Q1 is turned on to supply power to the subsequent circuit, which is used to charge the lithium battery and supply power for the charging status display during charging.

[0068] Figure 7 It is the adapter power supply / USB communication circuit. When the adapter is powered, only charging operation is performed; when the J5 connector is connected to the computer, the signals USB_DM and USB_DP will communicate with the computer via USB2.0, which is used to upload pictures or upgrade programs; the signal VUSB is the +5V voltage provided by the power adapter or the USB power supply end. The diode D8 and the diode D12 are connected between the J5 connector and the filter L3, and the capacitor C41 is connected between the J5 connector and the ferrite bead FB1, and the ferrite bead FB1 is connected to the capacitor C10. The filter L3 suppresses common-mode interference, suppresses electromagnetic wave radiation, attenuates EMI signals, suppresses differential-mode interference, and is connected to the MCU and communicates with it via USB2.0; the diodes D8 and D12 are used to protect electronic equipment from damage caused by electrostatic discharge.

[0069] In one embodiment, connector J5 is connected to the Type-C adapter board PCA, and the USB power supply / adapter power supply is filtered through capacitor C41, then jumpered through magnetic bead FB1 to become the power signal VUSB, and filtered through capacitor C10; the USB2.0 signal communicates with the MCU after passing through the L3 common-mode inductor, and is used to communicate with the computer, perform program upgrades, change interface images, etc.; the ESD tube is used to protect the USB power supply / adapter power supply and USB2.0 signals, and enhance the protection against static electricity.

[0070] Figure 8 It is a battery power detection circuit. As the battery power increases or decreases, the sampled voltage will also increase or decrease, and power detection is performed on this. The signal VIN is the signal on the key detection circuit, which is used for battery power sampling. The signal ADC_BAT is the sampling signal, which is transmitted to the MCU for ADC acquisition.

[0071] The signal VIN on the key detection circuit is transmitted to the resistor R84, the resistor R84 is connected to the resistor R64, the resistor R84 is connected to the capacitor C37, and the signal ADC_BAT is output between the resistor R84 and the resistor R64. The signal ADC_BAT is transmitted to the MCU to convert the analog signal into a digital signal. That is, the signal VIN is divided by the resistors R84 and R64, and the signal ADC_BAT is output through sampling. In one embodiment, the lithium battery is fully charged at 4.2V, and it is considered to be insufficient if it is lower than 3.6V; the voltage value of ADC_BAT is equal to R64 / (R84+R64), and the MCU samples and detects the signal. The voltage value range of ADC_BAT is between 4.2V and 3.6V.

[0072] Fig. 9 It is a battery charging circuit, which is used to charge the battery and indicate the charging status (charging, fully charged). Signals U3_CHRG and U3_DONE are charging status detection. U3_CHRG outputs a low level when charging; U3_DONE outputs a low level when fully charged; signal VUSB is a signal on the adapter power supply / USB communication circuit; signal U3_BAT is a signal on the battery reverse protection circuit, in which voltage detection and charging are performed. The signal VUSB on the adapter power supply / USB communication circuit is transmitted to U3_CHRG through resistor R25 and light-emitting diode D7, and U3_CHRG outputs a low level when charging; the signal VUSB on the adapter power supply / USB communication circuit is transmitted to U3_DONE through resistor R42 and light-emitting diode D3, and U3_DONE outputs a low level when charging. The charging chip U3 is connected to resistor R23, resistor R25, resistor R24, light-emitting diode D3 and light-emitting diode D7. The function of U3_CHRG is to detect the charging status of the signal pin. When the chip is charging the battery, the signal will output a low level.

[0073] The circuit connection relationship is: the power signal VUSB is connected to the charging input pin of the U3 chip, the signal U3_BAT is the battery end signal, R23 is the current limiting resistor of the charging current, R25 and R42 are the current limiting resistors of the LED lights D3 and D7 respectively, and the signals U3_CHRG and U3_DONE are the feedback pins of the charging status. When fully charged, the LED light D3 will light up, and the LED light D7 will not light up; when charging, the LED light D7 will light up, and the LED light D3 will not light up.

[0074] like Fig.10As shown, the key function circuit is composed of the key board PCA, which detects the level status of the five keys and realizes the corresponding functions, such as power on / off, left, right, confirmation, return and measurement start. The connector interface of the four keys is connected to the key board PCA; the signal POW_SW, signal K2, signal K3, and signal K4 are all key signals of the key board PCA. The MCU performs voltage detection on these four signals and realizes the corresponding functions of confirmation, left shift, right shift, return, power on, and power off. The J4 connector is connected to the ferrite bead FB6, resistor R48, resistor R27, and resistor R37, and outputs the signal POW_SW, signal K2, signal K3, and signal K4.

[0075] The keypad PCA is used for function selection, such as confirmation, left shift, right shift, power on / off, return, measurement and other function settings. The measurement circuit includes a key detection circuit, a first key detection circuit, a second key detection circuit, a DC / DC buck circuit, and a DC / DC boost circuit.

[0076] The circuit connection relationship is: connector J4 is connected to the key board PCA, R48\27\37 are pull-up resistors of signals K3\K2\K4 respectively, which force the level to be pulled high when the key is not pressed. When the corresponding key is pressed, the signal of the corresponding key will send a low-level signal to the MCU; signal POW_SW is the key signal of the power on or confirmation key function, which will send a high-level signal to the subsequent circuit when pressed; signal BAT is the power supply voltage, and the magnetic bead FB6 jumpers the signal BAT and the key board PCA, and reduces the high-frequency noise and spike interference on the power supply.

[0077] Fig.11 It is another key detection circuit. When the adapter or USB is connected to power supply, the power signal VUSB pulls the base of transistor Q9 to a high level and turns on the transistor Q9, thereby pulling the base of transistor Q10 to a low level, turning on transistor Q10, and then pulling the base of transistor Q3 to a high level. After transistor Q3 is turned on, the gate of MOS tube Q2 is pulled to a low level, and MOS tube Q2 is turned on; signal BAT is connected across signal VIN, capacitor C12 is the filter capacitor of signal BAT, and capacitors C13 / C14 are the filter signals of signal VIN.

[0078] When only the lithium battery is connected, when the power button is long pressed, POW_SW is high level, the transistor Q12 is turned on through the base of the transistor Q12, and a low level signal is transmitted to the MCU to determine whether the button is pressed or not; and the MCU keeps outputting the signal POW_ON as high level until the sleep time is reached or the power button is long pressed again, the signal is low level, and the shutdown operation is performed (when the button is in the power-on state, a short press serves as the confirmation key function).

[0079] In one embodiment, POW_SW is a signal of a key detection circuit.

[0080] 1. When the button is pressed, the signal is high level, which turns on the transistor of Q3, and then turns on the MOS tube of Q2, so that the signal BAT is converted into the signal VIN to supply power to the subsequent circuit; 2. When the button is pressed, the signal is high, turning on the transistor of Q12, and POW_SW_IN is low. The MCU will detect the high and low levels of the signal. When the signal is detected, POW_ON will be output as high level.

[0081] 3. VUSB is the signal on the adapter power supply / USB communication circuit. VUSB inputs a high level to the transistor of Q9. After it is turned on, the transistor of Q10 is turned on, and then the transistor of Q3 is turned on, and then the MOS tube of Q2 is turned on, so that the signal BAT is transferred to the signal VIN to power the subsequent circuit.

[0082] In this embodiment, transistor Q9 is connected to resistor R39, resistor R39 is connected to transistor Q10, transistor Q10 is connected to diode D4 and resistor R40, diode D4 is connected to transistor Q3, transistor Q3 is connected to transistor Q2 and resistor R24, resistor R24 ​​is connected to capacitor C12, transistor Q2 is connected to capacitor C13 and capacitor C14. The POW_SW is a signal of the key detection circuit transmitted to transistor Q12, transistor Q12 is connected to resistor R67, and outputs a POW_SW_IN signal.

[0083] Fig.12 It is another key detection circuit, which is used to detect keys and implement corresponding detection functions, such as shutdown and shutdown detection functions and information or function confirmation. In addition, this key detection circuit is used for the power-on function of the medical rebound tonometer. When the medical rebound tonometer is turned off, long pressing this key will turn on the device. When the key SW1 is not pressed, the K1 signal is pulled up to a high level by the R20 resistor, and it is detected as not pressed; when the key SW1 is pressed, the K1 signal is a low level, and the MCU detects the low level and determines that the key SW1 has been pressed.

[0084] like Fig.12 As shown, the key detection circuit detects the key and implements the corresponding measurement function. Press the key SW1 to perform the intraocular pressure test. When the key SW1 is pressed, the signal K1 outputs a low level, and the MCU detects the high and low levels of the signal to control the probe coil circuit. The touch switch SW1 is connected to the resistor R20.

[0085] Fig.13It is a DC / DC buck circuit. The signal VIN is connected to the power input terminal of the DC / DC buck chip U4 through the magnetic bead FB8. The enable pin of the buck chip U4 is pulled up to the power input terminal of the buck chip U4 through R28, and the buck chip U4 is started to perform buck work. The inductor L1 is used for energy storage and filtering. The resistors R29 and R30 are used to configure the output voltage of the buck chip U4. The intersection of the two resistors is connected to the feedback pin of the buck chip U4. The relationship between the output voltage and the resistors R29 and R30 is: Vout=0.6V*(1+R29 / R30), where 0.6V is the feedback voltage of the buck chip U4 when it works normally, and the capacitors C15\C16\C18\C19 are filter capacitors.

[0086] Fig.14 It is a DC / DC boost circuit, which boosts the voltage of the energy supply unit. Further, the DC / DC boost circuit boosts the VIN signal on the first button detection circuit to 5.2V to provide corresponding power supply for subsequent circuits, such as the probe coil control circuit.

[0087] The boost chip U5 is connected to the ferrite bead FB7, the capacitor C20, the capacitor C21, the resistor R31, the inductor L2, the capacitor C22, the resistor R32, the resistor R33, the capacitor C23, and the capacitor C24.

[0088] Fig.14 In the figure, the signal VIN is connected to the power input terminal of the DC / DC boost chip U5 through the magnetic bead FB7, the enable pin of the boost chip U5 is pulled up to the power input terminal of the boost chip U5 through the resistor R31, and the boost chip U5 is started to perform the boost operation. The switch pin of the boost chip U5 is connected to the power input terminal of the boost chip U5 through the inductor L2, the resistors R32 and R33 are used to configure the output voltage of the boost chip U5, and the intersection of the two resistors is connected to the feedback pin of the boost chip U5. The relationship between the output voltage and the resistors R32 and R33 is: Vout=1.23V*(1+R32 / R33), where 1.23V is the feedback voltage of the boost chip when it is working normally, and the capacitors C20\C21\C23\C24 are filter capacitors.

[0089] like Fig.15 The probe coil connection interface shown is used to connect the probe's action coil (including the head coil and the tail coil); L1+ and GND are the head coil signal pins, L2+ and L2- are the tail coil signal pins, and L2+ and L2- will process the collected signals through the intraocular pressure sampling circuit.

[0090] The L1+ signal pin of the J1 connector is connected to the diode D11, and the L2+ and L2- signal pins of the J1 connector are connected to the diode D9. The probe coil connection interface is used to connect the probe coil. Connector J1 connects the head coil and the tail coil, L1+ is the driving signal of the head coil, and L2+\L2- is the driving signal of the tail coil; D9 and D11 are ESD tubes to protect the signal from damaging the device.

[0091] When the probe passes through the tail coil, L2+ and L2- will produce current changes, and then the signal is amplified by the op amp chip.

[0092] Fig.16 For the L1 coil control circuit, the MCU applies a high level control signal L1OUT, which turns on the triode of Q5, and then turns on the MOS tube of Q4, energizes the L1 coil, and pops out the probe; the signal on the probe coil connection interface, L1+ and GND are the head coil signal pins. Transistor Q5 is connected to resistor R36, resistor R36 is connected to ferrite bead FB14, transistor Q4 is connected to ferrite bead FB14, transistor Q5, resistor R35, resistor R35 is connected to capacitor C43 and diode D5.

[0093] In one embodiment, the base of transistor Q5 is controlled by signal L1OUT (MCU controls the signal, and when the L1OUT signal output is high level, transistor Q7 is turned on). After transistor Q5 is turned on, the gate of MOS transistor Q4 is pulled to a low level, and MOS transistor Q4 turns on a 5.2V voltage signal to drive the head coil through resistor R35. At this time, coil L1 has a current from L1+ to GND to drive the coil; capacitor C43 filters the L1+ signal, and Schottky diode D6 plays a freewheeling role.

[0094] Fig.17 For the L2 coil control circuit, the MCU applies a high level to the control signal L2OUT, and the transistors and MOS tubes of Q8, Q7, and Q6 are turned on, which will energize the L2 coil and suck the probe back; and to detect the probe signal, the tail coil will be electromagnetized in advance. When the probe pops out and passes through the magnetized tail coil, a current signal that cuts the magnetic field will be generated; the signal on the probe coil connection interface, L2+ and L2- are the tail coil signal pins.

[0095] The high-level control signal L2OUT passes through transistor Q8, transistor Q7, and transistor Q6. A resistor R38 and a ferrite bead FB16 are connected in series between transistor Q7 and transistor Q6. A diode D6 is connected between the signal pin L2+ and the signal pin L2-.

[0096] In one embodiment, the base of the transistor Q7 is controlled by the signal L2OUT (MCU controls the signal, and when the L2OUT signal output is high, the transistor Q7 is turned on). After the transistor Q7 is turned on, the gate of the MOS transistor Q6 is pulled to a low level, and the MOS transistor Q4 conducts a 5.2V voltage signal to drive the L2+ signal of the tail coil; the gate of the MOS transistor Q8 is controlled by the signal L2OUT (MCU controls the signal, and when the L2OUT signal output is high, the MOS transistor Q8 is turned on), and the L2- signal of the tail coil is pulled low. At this time, the coil L2 has a current from L2+ to L2- to drive the coil, and the Schottky diode D6 plays a freewheeling role.

[0097] Fig.18 It is an intraocular pressure sampling circuit, which samples and amplifies the current signal (L2+, L2-) generated by the probe through the tail coil, and finally samples the obtained analog signal by the MCU; U1_VO: Samples and amplifies the current signal (L2+, L2-) generated by the probe through the tail coil; U2_INA+: electrical signal parameters obtained by voltage division by R11, R10, and R12; U1_REF: is the output signal of channel A of U2 chip, used for the negative input of channel B; U2_INB+: It is the signal obtained after U1_VO passes through the resistor, and is used for the positive input of channel B; VOUT: The signal obtained by U2_OUTB through the resistor, which is collected by MCU through ADC U2_OUTB: the final acquired signal; Chip U1 is connected to resistor R1, resistor R2, resistor R3, resistor R4, resistor R5, resistor R6, resistor R7, resistor R8, resistor R9, capacitor C1, capacitor C2, capacitor C3 and capacitor C4, resistor R11 is connected to resistor R10, resistor R10 is connected to resistor R12, capacitor C8 is connected to resistor R15, resistor R16 and resistor R17, and chip U2 is connected to capacitor C5, capacitor C6, capacitor C7, capacitor C9, resistor R13 and resistor R14. The L2+ signal passes through resistor R1, and then is filtered by capacitors C1\C3 and input to the inverting input pin of the op amp chip IC; resistors R3\R4 are 5V voltage, which is divided by these two resistors to produce 2.5V, which is the bias voltage of the signal); the L2- signal passes through resistor R2, and then is filtered by capacitors C2\C3 and input to the non-inverting input pin of the op amp chip IC; resistors R5\R6 are 5V voltage, which is divided by these two resistors to produce 2.5V, which is the bias voltage of the signal.

[0098] R7\R8\R9 are the gain adjustment resistors of the op amp chip; U1_VO is the output signal of the op amp chip and is connected to the pin of the in-phase input of the B channel of the op amp chip U2 through resistors R16 and R17; the signal U1_REF is provided by the output interface of the A channel of the op amp chip U2, which is the output reference voltage of the op amp chip U1 and the inverting input signal of the B channel of the op amp chip U2; the in-phase input signal U2_INA+ of the A channel is obtained by voltage division by resistors R10, R11, and R12, and is connected to the in-phase input of the A channel, and the output U1_REF also needs to be negatively fed back to the inverting input; the U2B channel of the op amp chip obtains the output signal U2_OUTB through the U1_REF and U2_INB+ signal inputs and outputs it to the ADC sampling interface of the MCU after passing through resistor R15.

[0099] Fig.19 It is a timer circuit that communicates with the MCU 2 C communication (signal I 2 C_SCL, I 2 C_SCL), and set the time, such as the year, month, day, hour, and minute; chip U15 is connected to capacitor 47, capacitor 48, SMD crystal resonator Y2, resistor R19, resistor R22, resistor R26 and diode R18, diode R18 is connected to ferrite bead FB12, and ferrite bead FB12 is connected to capacitor 38. Crystal oscillator Y2, capacitor C47 and capacitor C48 are the external clocks of clock chip U15; U3_BAT is the positive voltage of the battery, which is filtered out by magnetic beads FB12 and capacitor C38, and then connected to the voltage input terminal of clock chip U15 through diode D10. The I2C communication interface of clock chip U15 passes through resistors R18 and R19 respectively, and then the signals I2C1_SCL (clock signal) and I2C1_SCL (data signal) are pulled up to 3.3V by resistors R22 and R26 respectively, and then connected to the I2C communication interface of MCU for I2C communication. 2 C communication.

[0100] Fig. 20 It is the Bluetooth and buzzer connection interface, which is used to connect the Bluetooth adapter board PCA and control the Bluetooth module and buzzer. The signals TXD and RXD are used to interact with the Bluetooth module, and the signal BUZZER is the control signal of the buzzer. The J2 connector is connected to the ferrite bead FB13. The J2 connector outputs the RXD signal and inputs the TXD signal and the BUZZER signal. Connector J2 is connected to the Bluetooth adapter board. The signals TXD and RXD are the signals for serial communication between the MCU and the Bluetooth module. The signal BUZZER is the control signal of the buzzer (the PWM signal is sent by the MCU). The 3.3V passes through the bead FB13 to power the Bluetooth adapter board.

[0101] Fig.21 It is an LCD connection interface, which is used to connect a 1.3-inch display screen to display measurement values, function selection, function setting and other functions. BL_ON is the backlight control signal of the 1.3-inch display screen, and the high level backlight turns on; the signals LCD_DC, LCD_CS, LCD_SCL, LCD_MOSI, and LCD_RES are SPI communication signals, which interact with the MCU and then control the display screen through SPI signals. The J6 connector is connected to the ferrite bead FB10, transistor Q14, resistor R46, resistor R47, capacitor C39, resistor R50, capacitor C50, and resistor R41, and the signals LCD_DC, LCD_CS, LCD_SCL, LCD_MOSI, and LCD_RES interact with the J6 connector.

[0102] The signal LED is the power supply signal for the positive electrode of the display backlight. The on and off of the display backlight is controlled by the conduction of the MOS tube Q14 (the signal BL_ON is sent by the MCU to the gate of the MOS tube Q14. When the signal is high, the negative electrode of the MOS tube Q14 that turns on the display backlight is connected to GND through the resistor R47). The signal VDD powers the display through the capacitor C39 and the magnetic bead FB10. The MCU and the display communicate via SPI through the signals LCD_DC, LCD_CS, LCD_SCL, LCD_MOSI, and LCD_RES. The clock signal LCD_SCL is used to suppress radiation and reduce interference through the resistor R50 and the capacitor C55. The chip select signal LCD_CS needs to be pulled down to GND through the resistor R41 first.

[0103] Fig. 22 It is a data storage circuit, which communicates with the MCU via SPI (signals FLASH_SCK, FLASH_MOSI, FLASH_CS, FLASH_MISO), and stores relevant data, such as pictures, fonts, etc. Chip U10 is connected to resistor R44, resistor R45, capacitor C40, and ferrite bead FB11; 3.3V is connected to the power supply pin of the FLASH chip through capacitor C40 and bead FB11; MCU and FLASH chip communicate via SPI via signals FLASH_CS, FLASH_MISO, FLASH_MOSI, and FLASH_SCK to store pictures, test data, etc.

[0104] Fig.23It is the main control MCU, controlling the work, data interaction, analog signal sampling, etc. of each peripheral. Controller U7 is connected to capacitor C49, capacitor C50, capacitor C51, capacitor C52, capacitor C53, capacitor C54, resistor R43, and resistor 49, and the patch crystal resonator Y1 is connected to capacitor 45 and capacitor 46. Controller U7 (MCU) is connected to capacitors C49\C50\C51\C52\C53\C54, capacitors C49\C50\C51\C52\C53\C54 filter the power signal of the MCU, and resistors R43\49 are connected to the BOOT0 and B00T1 pins of the MCU.

[0105] In addition, crystal oscillator Y1 and capacitors C45 and C46 are external clocks of MCU, which are connected to MCU through signals OSC1 and OSC2. Signal L1OUT: control signal of the head coil; Signal L2OUT: control signal of the tail coil; Signal VOUT: acquisition signal of measurement data; Signal I2C1_SDA, I2C_SCL: I2C communication signal Signal USB_DM, USB_DP: USB2.0 communication signal Signals K1, K2, K3, K4: key signals, the level is low when pressed; Signal TXD, signal RXD: signals for serial communication with the Bluetooth module; Signals FLASH_CS, FLASH_MISO, FLASH_MOSI, FLASH_SCK: signals for SPI communication with the FLASH chip; Signals LCD_DC, LCD_CS, LCD_SCL, LCD_MOSI, LCD_RES: signals for SPI communication of the display; Signal BL_ON: display backlight control signal; Signals W_RST, SWDIO, SWCLK: MCU burning and simulation signals; Signal U3_DONE, U3_CHRG: status feedback signal of battery charging status; Signal ADC_BAT: battery power detection signal; Signal POW_ON: power supply control signal; Signal POW_SW_IN: power on / confirm key signal; Signal BUZZER: Buzzer control signal.

[0106] In an embodiment of the present invention, a staff member turns on the power supply, the energy supply unit supplies power to the entire system, the MCU module collects and controls signals from the key function module and the display function module, the date and function selection options are displayed on the 1.3-inch display screen, the probe is installed, and the key board PCA module is used to make selections, such as using the measurement button for data collection; the tail coil sucks back the probe and performs algorithm calculations, and the intraocular pressure measurement circuit calculates the obtained data through an algorithm according to the voltage change, thereby obtaining intraocular pressure data.

[0107] In summary, the single-coil excited medical rebound tonometer of the present invention is mainly used to measure the intraocular pressure parameters of patients. The device mainly includes a housing, a probe assembly, a forehead support assembly, a central processing unit for collecting and processing signals, and a display screen. The control circuit system includes a charging and energy supply unit power detection circuit, a key function circuit, and a measurement circuit.

[0108] The beneficial effects of the present invention are: proposing a portable intraocular pressure measuring device with a wide range of uses, no need for anesthesia for patients, and simple measurement; the present invention solves the problems of the prior art solutions requiring anesthesia for patients and complicated operation, and the operation is simple, the measurement is faster, and the cost is lower.

[0109] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A single-coil excited medical rebound tonometer, characterized in that: It comprises a housing (1), a probe assembly (4), a central signal processing unit (7) and an interactive display unit (5); The housing (1) is used to provide body protection and support for a medical rebound tonometer with single coil excitation; The probe assembly (4) is used to eject the probe and contact the measurement target, and with the help of the reverse action of the measurement target, the rear of the probe rebounds into the measurement cavity of the tonometer; The central signal processing unit (7) is used for collecting and processing signals, and for detecting, receiving and processing voltage changes on the single excitation coil to calculate the intraocular pressure of the measurement target; The interactive display unit (5) is used to display the working state of the single-coil excited medical rebound tonometer and the intraocular pressure data calculated by the central processing unit (7), and to receive external input control signals.

2. A single-coil excited medical rebound tonometer according to claim 1, characterized in that: The single excitation coil is either the head coil or the tail coil.

3. A single-coil excited medical rebound tonometer according to claim 2, characterized in that: It further comprises a forehead support component (2) and an energy supply unit (6); The forehead support assembly is used to support or abut against the support body to adjust the distance between the front of the probe and the target to be measured; the forehead support assembly further comprises a dial wheel (3), and the dial wheel (3) is rotated to push the forehead support assembly forward and backward through the spiral support member; The energy supply unit (6) provides power for rotating the dial and electricity for exciting the components.

4. A single-coil excited medical rebound tonometer according to claim 1, characterized in that: The probe assembly comprises a probe (13), a probe base (14), a cartridge case (15), a head coil (16) and a tail coil (18); one of the head coil and the tail coil realizes magnetization of the tail portion of the probe (17) and collects signals based on the principle of electromagnetic induction, and the other coil ejects the probe and pulls back the probe.

5. A single-coil excited medical rebound tonometer according to claim 4, characterized in that: The probe pops out and bounces back after touching the eyeball. The change in probe speed causes the change in the electrical signals of the head coil and the tail coil. The electrical signal parameters are converted into intraocular pressure parameters by detecting the changes in the electrical signals of the head coil and the tail coil and processing the signals.

6. A single-coil excited medical rebound tonometer according to claim 5, characterized in that: Only one coil is used at the same time to measure the magnetization of the probe and the electrical signal parameters.

7. A single-coil excited medical rebound tonometer according to claim 6, characterized in that: When the probe is installed in the device, the probe is in a non-magnetized state; when the energy supply unit is turned on and the probe is excited by the single excitation coil, the probe is magnetized.

8. A single-coil excited medical rebound tonometer according to claim 7, characterized in that: When the energy supply unit is turned on and the probe is magnetized by the excitation coil, the magnetic material at the end of the probe is magnetized by the energized excitation coil.

9. A single-coil excited medical rebound tonometer according to claim 8, characterized in that: After pressing the measurement button, the head coil or tail coil is powered off and the magnetization excitation is terminated. A forward excitation signal is applied to the head coil. The probe is attracted by the magnetic field formed by the power supply of the head coil and impacts the eyeball. After the probe is ejected and contacts the eyeball, it rebounds.

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