High-frequency ultrasonic coining device for in-vitro measurement of cornea biomechanical properties

Abstract

The utility model relates to a high-frequency ultrasonic coining device for in-vitro measurement of cornea biomechanical properties. The high-frequency ultrasonic coining device comprises a test platform, a motion control mechanism, a force transducer, an adapter, an ultrasonic transducer and a computer, a motion control mechanism is installed on the test platform, a force transducer is installed on the motion control mechanism and connected with an ultrasonic transducer through an adapter, the output end of the ultrasonic transducer is a coining head, and the coining head faces a test in-vitro eyeball fixedly arranged below the coining head. And the computer is electrically connected with the force transducer, the ultrasonic transducer and the motion control mechanism respectively. According to the high-frequency ultrasonic coining device, ultrasonic coining is carried out on the to-be-tested in-vitro eyeball by integrating the ultrasonic transducer and the force measuring sensor, echo data and external pressure data on the to-be-tested in-vitro eyeball are measured in real time in the coining process, the echo data and the external pressure data are received by the computer, and the high-frequency ultrasonic coining device is used for detecting the external pressure of the to-be-tested in-vitro eyeball. Therefore, research data is provided for diagnosis and treatment of ophthalmic diseases.

Description

Technical Field

[0001] The utility model relates to the technical field of corneal biomechanical property testing, in particular to a high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties. Background Art

[0002] The cornea is a transparent layer of tissue located at the front of the eyeball. It protects the intraocular tissues and is the eye's primary refractive medium, accounting for approximately 70% of the eye's total refractive power. This means that even slight changes in corneal morphology can lead to significant changes in the optical properties of the entire eye. The biomechanical properties of the cornea play an important role in maintaining corneal morphology and transparency, designing refractive surgery, and developing artificial corneas. They are also highly correlated with many corneal pathologies, especially corneal ectasia diseases such as keratoconus, corneal marginal degeneration, and iatrogenic corneal ectasia after corneal refractive surgery. Therefore, measuring the biomechanical properties of the cornea is of great significance for the diagnosis and treatment of these diseases.

[0003] Therefore, there is an urgent need to provide a high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties. Utility Model Content

[0004] (1) Technical issues to be resolved

[0005] The technical problem to be solved by the present invention is to provide a high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties, so as to obtain biomechanical property parameters of the in vitro cornea and provide research data for the diagnosis and treatment of ophthalmic diseases.

[0006] (2) Technical solution

[0007] In order to achieve the above-mentioned purpose, the main technical solutions adopted by this utility model include:

[0008] The embodiment of the utility model provides a high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties, comprising a test platform, a motion control mechanism, a force sensor, an adapter, an ultrasonic transducer, and a computer;

[0009] The motion control mechanism is installed on the test platform, the force sensor is installed on the motion control mechanism, the detection end of the force sensor is connected to the ultrasonic transducer through the adapter, the output end of the ultrasonic transducer is an indentation head, and the indentation head is directed toward the in vitro eyeball to be tested fixed below it, and the computer is electrically connected to the force sensor, the ultrasonic transducer and the motion control mechanism respectively;

[0010] The motion control mechanism is used to drive the ultrasonic transducer to approach or move away from the isolated eyeball to be tested so that the indentation head can indent the isolated eyeball to be tested. The ultrasonic transducer transmits ultrasonic waves and pressure to the isolated eyeball to be tested through the indentation head and detects echo data. The force sensor is used to detect the external pressure applied to the isolated eyeball to be tested. The computer is used to receive the echo data detected by the ultrasonic transducer and the pressure data detected by the force sensor.

[0011] Optionally, the diameter of the indentation head is 2-3 mm, the distance between the position of the indentation head when it contacts the ex vivo eyeball to be tested and the position of the indentation head when it indents the ex vivo eyeball to be tested is 1-2 mm, and the motion control mechanism can provide a speed of 10-200 mm / min for driving the indentation head to perform indentation.

[0012] Optionally, a data acquisition module electrically connected to the force sensor and the ultrasonic transducer is provided inside the computer.

[0013] Optionally, the in vitro eyeball to be tested is an artificial eyeball, and the artificial eyeball includes an artificial anterior chamber and a corneal phantom;

[0014] The artificial anterior chamber is fixedly arranged below the indentation head. The corneal phantom is a silicone phantom. The center of the corneal phantom is a spherical protrusion with the same shape as the human cornea. The edge of the spherical protrusion extends outward to form a connecting portion. The connecting portion is fixedly arranged on the artificial anterior chamber, and the corneal phantom and the artificial anterior chamber enclose a cavity, and physiological saline is injected into the cavity.

[0015] Optionally, it further comprises an intraocular pressure control component, the intraocular pressure control component comprising an injection pipeline, a column water level gauge and an intraocular pressure regulating component electrically connected to the computer;

[0016] A through hole is opened on the artificial anterior chamber, one end of the injection pipeline is connected to the through hole, and the other end of the injection pipeline is divided into two branches, one branch is connected to the intraocular pressure regulating component, and the other branch is connected to the columnar water level gauge.

[0017] Optionally, a liquid pressure sensor is provided on the artificial anterior chamber, and a testing end of the liquid pressure sensor is connected to the interior of the artificial anterior chamber.

[0018] (3) Beneficial effects

[0019] The beneficial effects of the present invention are as follows: the high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties of the present invention comprises a test platform, a motion control mechanism, a force sensor, an adapter, an ultrasonic transducer and a computer; the motion control mechanism is installed on the test platform, the force sensor is installed on the motion control mechanism, the detection end of the force sensor is connected to the ultrasonic transducer through the adapter, the output end of the ultrasonic transducer is an indentation head, the indentation head faces the in vitro eyeball to be tested fixed thereunder, the computer is electrically connected to the force sensor, the ultrasonic transducer and the motion control mechanism respectively; the motion control mechanism is used to drive the ultrasonic transducer to approach or move away from the in vitro eyeball to be tested, so that the indentation head indents the eyeball to be tested. To test the ex vivo eyeball, the ultrasonic transducer transmits ultrasonic waves and pressure to the ex vivo eyeball to be tested through the indentation head and detects echo data. The force sensor is used to detect the external pressure on the ex vivo eyeball to be tested. The computer is used to receive the echo data detected by the ultrasonic transducer and the pressure data detected by the force sensor. Compared with the existing technology, the high-frequency ultrasonic indentation device of the present invention integrates the ultrasonic transducer and the force sensor to perform ultrasonic indentation on the ex vivo eyeball to be tested, and during the indentation process, the echo data and external pressure data on the ex vivo eyeball to be tested are measured in real time. The computer receives the above echo data and external pressure data, thereby providing research data for the diagnosis and treatment of ophthalmic diseases. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] Figure 1 This is a schematic structural diagram of Example 1 of a high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties of the present invention;

[0021] Figure 2 Schematic top view of the corneal phantom of Example 1 of the high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties of the present invention;

[0022] Figure 3 for Figure 2 Schematic cross-sectional view of the corneal phantom at AA.

[0023] [Description of Reference Numerals]

[0024] 1: Computer; 2: Motion control mechanism; 3: Force sensor; 4: Adapter; 5: Ultrasonic transducer; 6: Ex vivo eyeball to be tested; 61: Artificial anterior chamber; 62: Corneal phantom; 621: Spherical protrusion; 622: Connecting part; 7: Intraocular pressure regulating component; 8: Liquid pressure sensor. DETAILED DESCRIPTION

[0025] In order to better explain the present invention and facilitate understanding, the present invention is described in detail below through specific implementation methods in conjunction with the accompanying drawings.

[0026] Example 1:

[0027] Reference Figure 1 、 Figure 2 and Figure 3 This embodiment provides a high-frequency ultrasonic indentation system for in vitro measurement of corneal biomechanical properties, including a test platform (not shown in the figure), a motion control mechanism 2, a force sensor 3, an adapter 4, an ultrasonic transducer 5 and a computer 1.

[0028] A motion control mechanism 2 is mounted on the test platform, and a force sensor 3 is mounted on the motion control mechanism 2. The detection end of the force sensor 3 is connected to an ultrasonic transducer 5 via an adapter 4. The output end of the ultrasonic transducer 5 is an indenter, which is directed toward an isolated eyeball 6 to be tested, which is fixed below it. A computer 1 is electrically connected to the force sensor 3, the ultrasonic transducer 5, and the motion control mechanism 2.

[0029] The motion control mechanism 2 is used to drive the ultrasonic transducer 5 to approach or move away from the isolated eyeball 6 to be tested, so that the indentation head can indent the isolated eyeball 6 to be tested. The ultrasonic transducer 5 transmits ultrasonic waves and pressure to the isolated eyeball 6 to be tested through the indentation head, and detects echo data on the isolated eyeball 6 to be tested. The force sensor 3 is used to detect the external pressure exerted on the isolated eyeball 6 to be tested. The computer 1 is used to receive the echo data detected by the ultrasonic transducer 5 and the external pressure data exerted on the isolated eyeball 6 to be tested.

[0030] The high-frequency ultrasonic indentation system for in vitro measurement of corneal biomechanical properties of this embodiment performs ultrasonic indentation on the in vitro eyeball 6 to be tested by integrating the ultrasonic transducer 5 and the force sensor 3. During the indentation process, the echo data and external pressure data of the in vitro eyeball 6 to be tested are measured in real time. The computer 1 receives the above echo data and external pressure data, thereby providing important reference information for the subsequent diagnosis, treatment and research of ophthalmic diseases.

[0031] It should be noted that, during the indentation process, the indentation head contacts the out-of-vivo eyeball 6 to be tested to achieve indentation. Since the force is mutual, the external pressure exerted on the out-of-vivo eyeball 6 to be tested and the resistance force exerted on the indentation head by the out-of-vivo eyeball 6 to be tested are equal in magnitude and opposite in direction. The resistance force exerted on the indentation head by the out-of-vivo eyeball 6 to be tested is transmitted to the detection end of the force sensor 3 via the ultrasonic transducer 5 and the adapter 4. In this way, the force sensor 3 can indirectly measure the external pressure exerted on the out-of-vivo eyeball 6 to be tested, and the adapter 4 only serves to mechanically connect the force sensor 3 and the ultrasonic transducer 5.

[0032] Furthermore, the diameter of the indenter is 2-3 mm, the distance between the position of the indenter in contact with the isolated eye 6 to be tested and the position of the indenter in contact with the isolated eye 6 to be tested is 1-2 mm, and the motion control mechanism 2 can provide an indentation speed of 10-200 mm / min. It should be noted that the computer 1 can control the motion control mechanism 2 to drive the ultrasonic transducer 5, thereby achieving control of the indentation depth, indentation speed, and measurement time of the indenter.

[0033] It should be noted that the present invention uses an ultrasonic transducer 5 to detect echo data on the isolated eyeball 6 to be tested, and a force sensor 3 to detect the external pressure exerted on the isolated eyeball 6 to be tested. The echo data and the external pressure data are transmitted to the computer 1. These are inherent properties of the ultrasonic transducer 5 and the force sensor 3 as conventional existing devices. The present invention only uses the inherent properties of the ultrasonic transducer 5 and the force sensor 3 to detect and transmit back data, and does not analyze or process the data.

[0034] Furthermore, the computer 1 is internally provided with a data acquisition module electrically connected to the force sensor 3 and the ultrasonic transducer 5. The data acquisition module has a sampling rate of 100-200 MS / s and a sampling accuracy of 10-14 bits. The purpose of the data acquisition module is to achieve synchronous acquisition of echo data and mechanical data.

[0035] In this embodiment, the in vitro eyeball 6 to be tested is an artificial eyeball, comprising an artificial anterior chamber 61 and a corneal phantom 62. The artificial anterior chamber 61 is fixedly positioned below the indenter head. The corneal phantom 62 is a silicone phantom. The center of the corneal phantom 62 is a spherical protrusion 621, shaped like a human cornea. The edges of the spherical protrusion 621 extend outward to form a connecting portion 622, which is fixed to the artificial anterior chamber 61. The corneal phantom 62 and the artificial anterior chamber 61 enclose a cavity, which is filled with saline.

[0036] Furthermore, the spherical convex portion of the corneal phantom 62 has a thickness of 0.45-0.5 mm, an outer surface curvature of 7-8 mm, and an inner surface curvature of 6-7 mm.

[0037] In this embodiment, the high-frequency ultrasonic indentation system for in vitro measurement of corneal biomechanical properties also includes an intraocular pressure control component for simulating human intraocular pressure. Intraocular pressure refers to the pressure generated by the interaction between the contents of the eye and the eye wall, which maintains the shape of the eye.

[0038] The intraocular pressure control assembly includes an injection line, a columnar water level gauge (not shown), an intraocular pressure regulating component 7 electrically connected to a computer 1, and a liquid pressure sensor 8. A through-hole is provided in the artificial anterior chamber 61. One end of the injection line connects to the through-hole in the artificial anterior chamber 61. The other end of the injection line branches into two branches: one connecting to the intraocular pressure regulating component 7 and the other connecting to the columnar water level gauge. Liquid pressure sensor 8 is also located in the artificial anterior chamber 61, with its testing end communicating with the interior of the artificial anterior chamber 61.

[0039] During use, the intraocular pressure regulating component 7 is used to control the liquid level of the column water level gauge to simulate changes in intraocular pressure. The control range of intraocular pressure is 10-30 mgHg, and the interval deformation range is 5 mgHg. The liquid pressure sensor 8 is used to measure the intraocular pressure of the isolated eyeball 6 in real time.

[0040] Example 2:

[0041] This embodiment provides another high-frequency ultrasonic indentation system for in vitro measurement of corneal biomechanical properties. Unlike Example 1, the in vitro eyeball 6 to be tested in this embodiment is an in vitro animal eye, such as an in vitro pig eye or rabbit eye. The in vitro pig eye and rabbit eye are obtained from a slaughterhouse and immediately placed in 0.7% saline at 4°C. To prevent corneal edema, corneal biomechanical properties must be measured within 6 hours of the in vitro pig eye or rabbit eye.

[0042] The rest of the details that are the same as those in Example 1 will not be repeated here.

[0043] In the description of this utility model, it should be understood that the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of the technical features indicated. Therefore, a feature specified as "first" or "second" may explicitly or implicitly include one or more of such features. In the description of this utility model, "plurality" means two or more, unless otherwise specifically defined.

[0044] In this utility model, unless otherwise specified or limited, the terms "installed," "connected," "connect," "fixed," etc. should be understood in a broad sense. For example, they can refer to fixed connection, detachable connection, or integration; mechanical connection, electrical connection; direct connection, or indirect connection through an intermediate medium; internal communication between two components, or interaction between two components. Those skilled in the art will understand the specific meanings of the above terms in this utility model based on specific circumstances.

[0045] In the present invention, unless otherwise expressly specified or limited, when a first feature is “above” or “below” a second feature, it may mean that the first and second features are in direct contact, or that the first and second features are in indirect contact through an intermediate medium. Moreover, when a first feature is “above,” “above,” or “above” a second feature, it may mean that the first feature is directly above or obliquely above the second feature, or simply means that the first feature is at a higher level than the second feature. When a first feature is “below,” “below,” or “below” a second feature, it may mean that the first feature is directly below or obliquely below the second feature, or simply means that the first feature is at a lower level than the second feature.

[0046] In the description of this specification, the description of the terms "one embodiment", "some embodiments", "embodiment", "example", "specific example" or "some examples" means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present utility model. In this specification, the schematic expressions of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner. In addition, those skilled in the art can combine and combine different embodiments or examples described in this specification and the features of different embodiments or examples without contradiction.

[0047] Although the embodiments of the present invention have been shown and described above, it can be understood that the above embodiments are illustrative and cannot be understood as limitations on the present invention. Ordinary technicians in this field can change, modify, replace and modify the above embodiments within the scope of the present invention.

Claims

1. A high-frequency ultrasonic indentation device for in vitro measurement of corneal biomechanical properties, characterized in that: It includes a test platform, a motion control mechanism (2), a force sensor (3), an adapter (4), an ultrasonic transducer (5) and a computer (1); The motion control mechanism (2) is installed on the test platform, the force sensor (3) is installed on the motion control mechanism (2), the detection end of the force sensor (3) is connected to the ultrasonic transducer (5) through the adapter (4), the output end of the ultrasonic transducer (5) is an indentation head, and the indentation head faces the in vitro eyeball (6) to be tested fixed below it, and the computer (1) is electrically connected to the force sensor (3), the ultrasonic transducer (5) and the motion control mechanism (2) respectively; The motion control mechanism (2) is used to drive the ultrasonic transducer (5) to approach or move away from the isolated eyeball (6) to be tested, so that the indentation head indents the isolated eyeball (6) to be tested; the ultrasonic transducer (5) transmits ultrasonic waves and pressure to the isolated eyeball (6) to be tested through the indentation head and detects echo data; the force sensor (3) is used to detect the external pressure applied to the isolated eyeball (6) to be tested; and the computer (1) is used to receive the echo data detected by the ultrasonic transducer and the pressure data detected by the force sensor (3).

2. The high-frequency ultrasonic embossing device according to claim 1, wherein: The diameter of the indentation head is 2-3 mm, the distance between the position of the indentation head when contacting the isolated eyeball (6) to be tested and the position of the indentation head when indenting the isolated eyeball (6) to be tested is 1-2 mm, and the motion control mechanism (2) can provide a speed of 10-200 mm / min for driving the indentation head to perform indentation.

3. The high-frequency ultrasonic embossing device according to claim 1, wherein: The computer (1) is internally provided with a data acquisition module electrically connected to the force sensor (3) and the ultrasonic transducer (5).

4. The high-frequency ultrasonic embossing device according to claim 1, wherein: The in vitro eyeball (6) to be tested is an artificial eyeball, and the artificial eyeball comprises an artificial anterior chamber (61) and a corneal phantom (62); The artificial anterior chamber (61) is fixedly arranged below the indentation head. The corneal phantom (62) is a silicone phantom. The center of the corneal phantom (62) is a spherical protrusion (621) having the same shape as the human cornea. The edge of the spherical protrusion (621) extends outward to form a connecting portion (622). The connecting portion (622) is fixedly arranged on the artificial anterior chamber (61). The corneal phantom (62) and the artificial anterior chamber (61) enclose a cavity, and physiological saline is injected into the cavity.

5. The high-frequency ultrasonic embossing device according to claim 4, characterized in that: It also includes an intraocular pressure control component, which includes an injection pipeline, a column water level gauge, and an intraocular pressure regulating component (7) electrically connected to the computer (1); A through hole is provided on the artificial anterior chamber (61), one end of the injection pipeline is connected to the through hole, and the other end of the injection pipeline is divided into two branches, one branch is connected to the intraocular pressure regulating component (7), and the other branch is connected to the columnar water level gauge.

6. The high-frequency ultrasonic embossing device according to claim 5, wherein: A liquid pressure sensor (8) is provided on the artificial anterior chamber (61), and a test end of the liquid pressure sensor (8) is communicated with the interior of the artificial anterior chamber (61).

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