An ophthalmic A-mode device

Abstract

This invention discloses an ophthalmic A-scan ultrasound device, relating to the field of ophthalmic A-scan ultrasound technology. The device is an ultrasound probe comprising a main body, on which a detection mechanism, a pressure sensing unit, and an adjustment mechanism are disposed. The detection mechanism is located at one end of the main body and is used for ultrasonic detection of corneal thickness and axial length. The pressure sensing unit is located within the detection mechanism and is used to monitor the pressure exerted by the detection mechanism on the cornea. The adjustment mechanism is disposed on the main body and is used to adjust the pressure exerted by the detection mechanism on the cornea. The ophthalmic A-scan ultrasound device provided by this invention allows the pressure sensing unit to monitor the pressure exerted by the detection mechanism on the cornea when the user operates the probe main body. At this time, the adjustment mechanism can adjust the pressure between the detection mechanism and the cornea to maintain the pressure exerted by the detection mechanism on the cornea within a certain range.

Description

Technical Field

[0001] This invention relates to the field of ophthalmic A-scan technology, specifically to an ophthalmic A-scan device. Background Technology

[0002] Ophthalmic A-scan ultrasound is a medical examination method that uses ultrasound technology to examine eye diseases. It can examine the shape, size, position, structure of the eyeball and various eye lesions. It can also be used to measure corneal thickness and axial length.

[0003] For example, the authorized patent with authorization announcement number CN104000624B, authorization announcement date of April 13, 2016, and title "An Ultrasonic Probe Adhered to the Ocular Surface for Axial Length Measurement" has an arc-shaped structure adapted to the ocular surface, consisting of three layers: upper, middle, and lower. The upper and lower layers are both hydrogel layers. This improves upon the shortcomings of previous tests, such as the need for anesthetics, the requirement for patients to lie down during the examination, and the potential for corneal compression. It actively measures the axial length, reduces patient anxiety, and improves the accuracy of ophthalmic A-scan ultrasound.

[0004] In existing technologies, when operating an A-mode ultrasound probe, the pressure exerted by the probe on the cornea inevitably causes corneal deformation, leading to measurement errors. Summary of the Invention

[0005] The purpose of this invention is to provide an ophthalmic A-scan ultrasound device to overcome the aforementioned shortcomings of the prior art.

[0006] To achieve the above objectives, the present invention provides the following technical solution:

[0007] An ophthalmic A-scan ultrasound device, which is an ultrasound probe, includes a main body, on which are disposed:

[0008] A testing mechanism located at one end of the main body and used for ultrasonic testing of corneal thickness and axial length;

[0009] A pressure sensing unit, located within the detection mechanism, is used to monitor the pressure exerted by the detection mechanism on the cornea.

[0010] An adjustment mechanism is provided on the main body and is used to adjust the pressure exerted on the cornea by the detection mechanism.

[0011] The aforementioned ophthalmic A-mode ultrasound device includes a detection mechanism comprising two hydrogel layers, with the pressure sensing unit located between the two hydrogel layers.

[0012] The aforementioned ophthalmic A-mode ultrasound device includes an adjustment mechanism comprising a sleeve, with the main body slidably connected within the sleeve, and a linear drive assembly for driving the main body to move axially along the sleeve.

[0013] In the aforementioned ophthalmic A-mode ultrasound device, the detection mechanism has two squeezing parts on the side away from the main body. When the main body approaches the cornea, the two squeezing parts move away from each other to force the upper and lower eyelids to open.

[0014] The aforementioned ophthalmic A-mode ultrasound device has an anti-slip layer on the outer wall of the extrusion section.

[0015] In the aforementioned ophthalmic A-mode ultrasound device, a handle is provided on the sleeve, and two movable rods are rotatably connected to the handle. A torsion spring is provided between the movable rods and the handle. One end of the movable rod is fixed to a compression part, and the other end is constructed with a through groove. A sliding groove is constructed on the handle. A slider is fixed to the outer wall of the sleeve, and the slider is located in both the sliding groove and the through groove.

[0016] In the aforementioned ophthalmic A-mode ultrasound device, a limiting groove is constructed on the handheld part, and a limiting block is constructed on the rotating shaft of the movable rod, with the limiting block located within the limiting groove.

[0017] The aforementioned ophthalmic A-mode ultrasound device includes a linear drive assembly comprising a rotating ring rotatably connected to a handheld part, an internal gear constructed on the inner wall of the rotating ring, a lead screw rotatably connected to a sleeve, a first connecting part fixed to the lead screw, a second connecting part rotatably connected inside the handheld part, the second connecting part being inserted into the first connecting part, a drive gear fixed to the second connecting part, the drive gear meshing with the internal gear, a drive block fixed to the outer wall of the main body, and the drive block being threadedly connected to the lead screw.

[0018] In the aforementioned ophthalmic A-mode ultrasound device, a locking mechanism is provided between the handheld part and the sleeve. After the two compression parts move away from each other, the locking mechanism locks the relative position of the handheld part and the sleeve.

[0019] The aforementioned ophthalmic A-mode ultrasound device includes a locking mechanism comprising a locking disc fixed to a movable rod, the locking disc having a locking groove, a locking rod slidably connected within the handheld part, a wedge-shaped portion at the top of the locking rod, a notch adapted to the wedge-shaped portion at the bottom of the rotating ring, and a spring provided within the handheld part for forcing the wedge-shaped portion into the notch.

[0020] In the above technical solution, the present invention provides an ophthalmic A-mode ultrasound device. When the user operates the probe body, the detection mechanism will contact the cornea of ​​the examinee and perform ultrasound detection on the corneal thickness and axial length. At this time, the pressure sensor unit can monitor the pressure exerted on the cornea by the detection mechanism. If the pressure is too high, it will cause corneal deformation of the examinee, which will affect the accuracy of the A-mode ultrasound detection. Therefore, an adjustment mechanism is set up to adjust the pressure between the detection mechanism and the cornea so that the pressure exerted on the cornea by the detection mechanism is kept within a certain range, thereby improving the accuracy of the A-mode ultrasound detection while minimizing corneal deformation. Attached Figure Description

[0021] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this invention. For those skilled in the art, other drawings can be obtained based on these drawings.

[0022] Figure 1 This is a schematic diagram of the detection mechanism structure provided in an embodiment of the present invention;

[0023] Figure 2 This is a schematic diagram of the sleeve structure provided in an embodiment of the present invention;

[0024] Figure 3 This is a schematic diagram of the movable rod structure provided in an embodiment of the present invention;

[0025] Figure 4 This is a schematic diagram of the limiting block structure provided in an embodiment of the present invention;

[0026] Figure 5 A cross-sectional view of the handheld part and the rotating ring provided in an embodiment of the present invention;

[0027] Figure 6 This is a schematic diagram of the cross-sectional structure of the sleeve provided in an embodiment of the present invention;

[0028] Figure 7 This is a schematic diagram of the locking disk structure provided in an embodiment of the present invention;

[0029] Figure 8 This is a schematic diagram of the locking disc structure provided in another embodiment of the present invention.

[0030] Explanation of reference numerals in the attached figures:

[0031] 1. Main body; 2. Detection mechanism; 201. Hydrogel layer; 3. Pressure sensing unit; 4. Sleeve; 5. Extrusion part; 6. Handheld part; 7. Movable rod; 8. Through groove; 9. Slide groove; 10. Slider; 11. Limiting groove; 12. Limiting block; 13. Rotating ring; 14. Internal gear; 15. Lead screw; 16. First connecting part; 17. Second connecting part; 18. Drive gear; 19. Drive block; 20. Locking disc; 21. Locking groove; 22. Locking rod; 23. Notch; 24. Wedge-shaped part; 25. Spring; 26. Stop block; 27. Abutment block. Detailed Implementation

[0032] To enable those skilled in the art to better understand the technical solution of the present invention, the present invention will be further described in detail below with reference to the accompanying drawings.

[0033] Reference Figure 1-8 This invention provides an ophthalmic A-mode ultrasound device, which is an ultrasound probe. The ultrasound probe includes a main body 1, on which a detection mechanism 2, a pressure sensing unit 3, and an adjustment mechanism are disposed. The detection mechanism 2 is located at one end of the main body 1 and is used to perform ultrasound detection of corneal thickness and axial length. The pressure sensing unit 3 is located inside the detection mechanism 2 and is used to monitor the pressure exerted by the detection mechanism 2 on the cornea. The adjustment mechanism is disposed on the main body 1 and is used to adjust the pressure exerted by the detection mechanism 2 on the cornea.

[0034] Specifically, the ultrasound probe is a crucial component of ophthalmic A-mode ultrasound. Users typically hold the probe and place the detection mechanism 2 at one end against the patient's cornea to perform ultrasound measurements of corneal thickness and axial length. This is existing technology and will not be elaborated upon. The innovation of this embodiment lies in the inclusion of a pressure sensing unit 3 within the detection mechanism 2 (the pressure sensing unit 3 can employ existing pressure sensors or similar structures, which will not be elaborated upon). When the detection mechanism 2 contacts the cornea, the pressure sensing unit 3 can monitor the pressure between the detection mechanism 2 and the cornea. Excessive pressure between the two can cause discomfort to the patient. If the pressure between the detection mechanism 2 and the cornea is too low, the two will not fit together properly, which will affect the accuracy of the A-mode ultrasound. When the pressure sensing unit 3 detects that the pressure between the detection mechanism 2 and the cornea is too low, the adjustment mechanism will slightly increase the pressure between the detection mechanism 2 and the cornea to make them fit together better. When the pressure sensing unit 3 detects that the pressure between the detection mechanism 2 and the cornea is too high, the adjustment mechanism will decrease the pressure between the detection mechanism 2 and the cornea to minimize the deformation of the cornea caused by compression and improve the accuracy of the A-mode ultrasound.

[0035] This invention provides an ophthalmic A-mode ultrasound device. When the user operates the probe body 1, the detection mechanism 2 contacts the cornea of ​​the examinee and performs ultrasound detection on the corneal thickness and axial length. At this time, the pressure sensor unit 3 can monitor the pressure exerted on the cornea by the detection mechanism 2. If the pressure is too high, it will cause corneal deformation, which will affect the accuracy of the A-mode ultrasound detection. Therefore, an adjustment mechanism is provided to adjust the pressure between the detection mechanism 2 and the cornea so that the pressure exerted on the cornea by the detection mechanism 2 is kept within a certain range, thereby improving the accuracy of the A-mode ultrasound detection while minimizing corneal deformation.

[0036] In another embodiment of the present invention, the detection mechanism 2 further includes two hydrogel layers 201, and the pressure sensing unit 3 is located between the two hydrogel layers 201. Specifically, in the prior art, to reduce the discomfort of the examinee, the detection mechanism 2 is generally provided with two hydrogel layers 201 to wrap the detection component. The detection component generally includes a focusing lens, a circuit layer, a connection layer, and an energy storage layer, etc., which is prior art and will not be described in detail. In this embodiment of the present invention, the pressure sensing unit 3 is placed between the two hydrogel layers 201. When the outer hydrogel layer 201 touches the cornea, the outer hydrogel layer 201 will exert a certain pressure on the pressure sensing unit 3. This is the pressure between the detection mechanism 2 and the cornea, which is used to adjust the pressure on the cornea in conjunction with the adjustment mechanism. It should be noted that the pressure sensing unit 3 may not be exactly equal to the pressure of the eye skin on the outer hydrogel layer 201, but the two pressures are proportional, so adjustment can still be made based on the pressure detected by the pressure sensing unit 3.

[0037] In another embodiment of the present invention, the adjusting mechanism includes a sleeve 4, the main body 1 is slidably connected inside the sleeve 4, and a linear drive assembly for driving the main body 1 to move axially along the sleeve 4. Specifically, when detecting the cornea, the user holds the sleeve 4 and operates the main body 1. When the main body 1 moves closer to the cornea, the detection mechanism 2 squeezes the cornea, increasing the pressure on the cornea. Conversely, when the main body 1 moves away from the cornea, the pressure on the cornea decreases. Therefore, a linear drive assembly is provided to drive the main body 1 to move along the sleeve 4. The sleeve 4 is hollow inside, allowing the main body 1 to slide. The linear drive assembly can be automatic, such as an electric push rod (not shown) in the prior art, with one end of the electric push rod fixed to the inner wall of the sleeve 4. The other end is fixed to the outer wall of the main body 1. When the pressure sensing unit 3 detects that the pressure on the cornea is too high, the electric push rod drives the main body 1 to move away from the cornea along the sleeve 4, thereby reducing the pressure on the cornea and minimizing the deformation caused by the pressure. When the pressure sensing unit 3 detects that the pressure on the cornea is too low, the electric push rod drives the main body 1 to move slightly closer to the cornea along the sleeve 4, thereby slightly increasing the pressure on the cornea. This makes the monitoring mechanism fit the cornea more closely, thereby improving the accuracy of A-mode ultrasound detection.

[0038] In another embodiment of the present invention, the detection mechanism 2 is provided with two squeezing parts 5 on the side away from the main body 1. When the main body 1 approaches the cornea, the two squeezing parts 5 move away from each other to force the upper and lower eyelids to open. Specifically, in the prior art, before the probe is used, the user needs to use their fingers to pull open the subject's upper and lower eyelids before the detection mechanism 2 can be placed against the cornea. In this embodiment of the present invention, the two squeezing parts 5 are used to simulate the user's two fingers. During use, the user directly holds the sleeve 4 and places the two squeezing parts 5 against the subject's upper and lower eyelids respectively. Then, the user directly controls the sleeve 4 to move closer to the subject's eyes. At this time, the two squeezing parts 5 will move away from each other and force the subject's upper and lower eyelids to open, thereby exposing the subject's cornea. The squeezing parts 5 stop operating when the detection mechanism 2 is about to touch the cornea. At this time, the adjustment mechanism can be operated to make the detection mechanism 2 touch the cornea and perform the detection. The outer wall of the squeezing part 5 is constructed with an anti-slip layer to increase the friction between the squeezing part 5 and the subject's eyelids, so that the squeezing part 5 can force the subject's eyelids to open with a smaller force, that is, the squeezing part 5 has a smaller impact on the cornea.

[0039] The two extrusion sections 5 can be driven by two sets of rotating structures such as motors. The two sets of motors can drive the two extrusion sections 5 to rotate synchronously and in opposite directions, that is, drive the two extrusion sections 5 to move away from each other. Preferably, the sleeve 4 is covered with a handhold 6, and two movable rods 7 are rotatably connected to the handhold 6. A torsion spring is provided between the movable rods 7 and the handhold 6. One end of the movable rod 7 is fixed to one of the extrusion sections 5, and the other end is constructed with a through groove 8. The handhold 6 is constructed with a sliding groove 9. A slider 10 is fixed to the outer wall of the sleeve 4. The slider 10 is located in both the sliding groove 9 and the through groove 8. Specifically, the pivot of the movable rod 7 and the pressing part 5 at one end of the movable rod 7 are located on both sides of the central axis of the main body 1. That is, when the pressing part 5 touches the eyes of the examinee, the main body 1 continues to move towards the eyes, which can force the movable rod 7 to compress the torsion spring and rotate around its pivot (the spring has a small elastic force and is only used to force the movable rod 7 to return to its original position. The torsion spring can also be replaced by an elastic sheet, which is existing technology and will not be described in detail). In this embodiment, the user controls the main body 1 through the handheld part 6. When the handheld part 6 moves towards the eyes of the examinee, the two pressing parts 5 first touch the upper and lower eyelids of the examinee respectively, and then the user controls the handheld part 6 to continue moving towards the eyes of the examinee. As the eye moves, the movable rod 7 compresses the torsion spring and rotates around its axis, causing the two compression parts 5 to rotate with the movable rod 7 away from the central axis of the main body 1. While the movable rod 7 rotates, the inner wall of the through groove 8 at its other end forces the slider 10 to move along the slide groove 9. That is, while the compression part 5 is under pressure and drives the movable rod 7 to rotate, the through groove 8 at the other end of the movable rod 7 forces the slider 10, the sleeve 4, and the main body 1 to move along the slide groove 9 towards the side closer to the eye. When the detection mechanism 2 on the main body 1 is about to touch the cornea, the movable rod 7 stops rotating, making it convenient to adjust the detection mechanism so that the detection mechanism 2 touches the cornea and performs the detection.

[0040] It should be noted that the rotation of the movable rod 7 has a certain range. Preferably, the handheld part 6 is constructed with a limiting groove 11, and the rotating shaft of the movable rod 7 is constructed with a limiting block 12, which is located in the limiting groove 11. Under the action of the torsion spring, the movable rod 7 drives the squeezing part 5 at one end to rotate to a position close to the detection mechanism 2. At this time, the limiting block 12 abuts against one end of the inner wall of the limiting groove 11. When the two squeezing parts 5 force the upper and lower eyelids of the examinee to open (that is, when the two squeezing parts 5 move away from each other to the extreme position), the movable rod 7 squeezes the torsion spring and causes the limiting block 12 to rotate to the other end of the limiting groove 11. In this way, the angle of rotation of the limiting block 12 and the movable rod 7 is limited by the limiting groove 11.

[0041] While the electric telescopic rod, based on the feedback automatic control of the pressure sensing unit 3, allows the main body 1 to move along the sleeve 4 conveniently, it has certain uncertainties. A malfunction could cause irreversible damage to the subject's cornea. Therefore, as an alternative to the aforementioned electric push rod, the preferred linear drive assembly includes a rotating ring 13 rotatably connected to the handheld part 6. The inner wall of the rotating ring 13 has an internal gear 14. A lead screw 15 is rotatably connected to the sleeve 4, and a first connecting part 16 is fixed to the lead screw 15. A second connecting part 17 is rotatably connected inside the handheld part 6, and the second connecting part 17 is inserted into the first connecting part 16. The second connecting part 17 and the first connecting part 16 can move axially relative to each other while transmitting rotational motion. This can be achieved through the sleeve connection of non-rotating bodies. A drive gear 18 is fixed to the second connecting part 17, meshing with the internal gear 14. A drive block 19 is fixed to the outer wall of the main body 1, and the drive block 19 is threadedly connected to the lead screw 15 (using a ball screw). Specifically, the screw 15, drive gear 18, and drive block 19 are symmetrically arranged in two or more sets to improve the stability of the main body 1's movement; the first connecting part 16 is constructed as a non-rotating body, and the second connecting part 17 has a connecting groove adapted to the first connecting part 16, that is, the first connecting part 16 and the second connecting part 17 can extend and retract relative to each other and rotate synchronously; the sleeve 4 has a connecting groove for the drive block 19 to slide; when it is necessary to drive the main body 1 to move along the sleeve 4, the rotating ring 13 is rotated to drive the two drive gears 18 to rotate synchronously and in the same direction through the internal gear 14, thereby driving the two second connecting parts 17 to rotate synchronously. Since the first connecting part 16 is inserted into the second connecting part 17, the rotation of the second connecting part 17 can drive the first connecting part 16 and the screw 15 to rotate synchronously and in the same direction. The screw 15 rotates in the direction of rotation. Since the screw 15 is threadedly connected to the drive block 19, the two screws 15 can drive the two drive blocks 19 to move synchronously along the sleeve 4 when they rotate synchronously, thereby driving the main body 1 to move along the sleeve 4. The purpose of this arrangement is that the rotating ring 13 is set on the handheld part 6 for easy operation by the user. The rotating ring 13 and the drive gear 18 are both set on the handheld part 6 and can transmit power to each other. The screw 15, drive block 19 and main body 1 are all located inside the sleeve 4, and the sleeve 4 and the handheld part 6 can move relative to each other. For this purpose, the first connecting part 16 and the second connecting part 17 are provided so that the sleeve 4 and the handheld part 6 maintain transmission while moving relative to each other, so as to ensure that the rotating ring 13 can drive the screw 15 to rotate at any time, thereby driving the drive block 19 and the main body 1 to move along the sleeve 4. When the user controls the movement of the main body 1 by holding the handpiece 6, the two squeezing parts 5 can move away from each other when squeezing the upper and lower eyelids and drive the main body 1 and sleeve 4 to move towards the side of the subject's eye. At this time, the detection mechanism 2 on the main body 1 will come into contact with the cornea. Then, by manually rotating the rotating ring 13, the main body 1 can be moved along the sleeve 4, so that the detection mechanism 2 on the main body 1 comes into contact with the cornea and performs ultrasound detection of corneal thickness and axial length.

[0042] Furthermore, a locking mechanism is provided between the handheld part 6 and the sleeve 4. After the two squeezing parts 5 move away from each other, the locking mechanism locks the relative position of the handheld part 6 and the sleeve 4. Specifically, when the two squeezing parts 5 move away from each other to their extreme positions (that is, when the corresponding limiting block 12 moves to one end of the limiting groove 11), the detection mechanism 2 is about to touch the cornea. At this time, the adjustment mechanism can be operated. However, the user needs to continuously overcome the force of the torsion spring. For this reason, a locking mechanism is provided. When the two squeezing parts 5 move away from each other to their extreme positions, that is, when the two squeezing parts 5 force the upper and lower eyelids of the examinee to separate, the relative position of the sleeve 4 and the handheld part 6 is locked by the locking mechanism. At this time, the movable rod 7 cannot be reset under the action of the torsion spring. The user only needs to control the handheld part 6 and make the two squeezing parts 5 continuously touch the upper and lower eyelids of the examinee to open them, which facilitates the subsequent operation of the adjustment mechanism.

[0043] Preferably, the locking mechanism includes a locking disc 20 fixed to the movable rod 7, the locking disc 20 having a locking groove 21, a locking rod 22 slidably connected inside the handheld part 6, a wedge-shaped part 24 at the top of the locking rod 22, a notch 23 at the bottom of the rotating ring 13 adapted to the wedge-shaped part 24, and a spring 25 inside the handheld part 6 forcing the wedge-shaped part 24 into the notch 23. Specifically, a movable groove is constructed along the length of the handheld part 6, the locking rod 22 is slidably connected in the movable groove, the spring 25 is located in the movable groove and sleeved on the locking rod 22, and both ends of the spring 25 are fixed to the outer wall of the locking rod 22 and the inner wall of the movable groove, respectively; the locking disc 20 is fixed to the rotating shaft of the movable rod 7, and the two are coaxially arranged, one end of the locking rod 22 abuts against the outer wall of the locking disc 20, and the other end is embedded in the notch 23; a stop block 26 is constructed at the bottom of the rotating ring 13; when the movable rod 7 rotates, the locking disc 20 simultaneously moves in the handheld part. When the two pressing parts 5 are moved away from each other to their extreme positions, the movable rod 7 and the locking disc 20 both rotate to a certain angle. At this time, the locking groove 21 on the locking disc 20 is set along the length direction of the handle 6, that is, the bottom of the locking rod 22 is not in contact with the outer wall of the locking disc 20, and it can enter the locking groove 21 under the action of external force. When the two pressing parts 5 are moved away from each other to their extreme positions, the rotating ring 13 is rotated, and the wedge-shaped part 24 at the top of the locking rod 22 is in contact with the inner wall of the notch 23 at the bottom of the rotating ring 13 (as shown). Figure 7As shown, the rotating ring 13 can drive the notch 23 to rotate to the left, so as to force the locking rod 22 to move downward through the inner wall of the notch 23, thereby forcing the locking rod 22 to squeeze the spring 25 and enter the locking groove 21, thereby locking the relative position of the handheld part 6 and the sleeve 4; after the locking rod 22 is inserted into the locking groove 21, the rotating ring 13 can be rotated to adjust the relative position of the main body 1 and the sleeve 4 until the detection mechanism 2 at one end of the main body 1 touches the cornea and performs ultrasound detection on the corneal thickness and axial length (the diameter of the rotating ring 13 is larger than the diameter of the drive gear 18, so that the rotating ring 13 can drive the drive gear 18 to rotate several times when it rotates once. When the wedge part 24 moves from the notch 23 to the position of the stop block 26, the rotating ring 13 cannot rotate, that is, the rotating ring 13 has a rotation range of less than 360 degrees. During its rotation, the main body 1 can be moved along the axial direction of the sleeve 4 through the drive gear 18 and the lead screw 15, thereby adjusting the position of the main body 1).

[0044] The advantage of this setup is that when the probe is idle, the rotating ring 13 is in its original position. At this time, the top of the locking rod 22 is embedded in the notch 23, and the bottom abuts against the outer wall of the locking disc 20. Thus, the rotating ring 13 can be locked by the locking rod 22, minimizing the rotation of the rotating ring 13. In this state, the squeezing part 5 and the movable rod 7 can rotate, that is, the two squeezing parts 5 can be moved away from each other to open the upper and lower eyelids of the examinee. When the two squeezing parts 5 are moved away from each other to their extreme positions, the detection mechanism 2 is about to touch the cornea. At this time, rotating the rotating ring 13 can force the locking rod 22 to squeeze the spring 25 and enter the locking groove 21, thereby limiting the relative position between the sleeve 4 and the handheld part 6. At the same time, the wedge-shaped part 24 at the top of the locking rod 22 moves out from the notch 23 and abuts against the bottom wall of the rotating ring 13. Then, by continuing to rotate the rotating ring 13, the relative position between the main body 1 and the sleeve 4 can be adjusted, thereby making the detection mechanism 2 touch the cornea and maintain a certain pressure on the cornea to accurately detect the corneal thickness and axial length using ultrasound.

[0045] The aforementioned locking mechanism is suitable for manual operation. When using it, the user can hold the handle 6 and place their palm on the subject's face to stabilize the basic position of the handle 6 and the main body 1. Then, by bringing the handle 6 close to the subject's eyes, the two squeezing parts 5 will move away from each other, thereby opening the subject's eyelids. At the same time, the user's other hand or a single finger can rotate the rotating ring 13 to lock the locking disc 20. Simultaneously, the detection mechanism 2 at one end of the main body 1 is driven to fit against the cornea and perform ultrasound detection of corneal thickness and axial length. Compared with the single-handed operation in the prior art (where the other hand needs to pry open the subject's eyelids), this method can more accurately control the pressure exerted on the cornea by the detection mechanism 2.

[0046] To further adapt to automated operation, the present invention provides another embodiment. Further, the locking mechanism includes a locking disc 20 fixed to a movable rod 7. One side of the locking disc 20 has a flat portion, and an abutment block 27 is formed on the flat portion. A locking rod 22 is slidably connected within the handle portion 6. A movable groove is formed within the handle portion 6 along its length, and the locking rod 22 is slidably connected within the movable groove. A wedge-shaped portion 24 is formed at the top of the locking rod 22. A notch 23 adapted to the wedge-shaped portion 24 is formed at the bottom of the rotating ring 13. A stop block 26 is formed at the bottom of the rotating ring 13. The handle portion 6... A spring 25 is provided inside, located in the movable groove and sleeved on the locking rod 22. The two ends of the spring 25 are respectively fixed to the outer wall of the locking rod 22 and the inner wall of the movable groove. The spring 25 is used to force the wedge-shaped part 24 into the notch 23. The locking disc 20 is fixed on the rotating shaft of the movable rod 7, and the two are coaxially arranged. The locking rod 22 and its planar surface are located on the same side of the locking disc 20. Specifically, in this embodiment, the drive gear 18 is driven by a micro motor (the driving method of the micro motor is prior art and not shown; it is mounted on the handheld part 6, and its output end is fixed to a drive gear 18). When the micro motor drives one drive gear 18 to rotate, the rotating ring 13 and the other drive gear 18 will rotate synchronously. In use, the micro motor directly drives the drive gear 18 and the rotating ring 13 to rotate. When the rotating ring 13 rotates, it can abut against the wedge-shaped part 24 through the inner wall of the notch 23 and cause the locking rod 22 to press against the spring 25, thereby causing the end of the locking rod 22 away from the wedge-shaped part 24 to press against the flat part, so as to force the locking disc 20, the movable rod 7 and the pressing part 5 to rotate (during this process, the drive gear 18 drives the lead screw 15 to rotate at a certain angle, that is, the main body 1 rotates along the sleeve 4). (Axial movement of a certain distance); With this configuration, when in use, the two squeezing parts 5 are placed on the eyelids of the examinee, and then the micro motor is started to drive the two squeezing parts 5 to move away from each other, so as to automatically open the eyelids of the examinee. Alternatively, after the two squeezing parts 5 move away from each other, the eyelids of the examinee can be opened first, and then the two squeezing parts 5 can squeeze and restrict the open eyelids. When the wedge-shaped part 24 moves out of the notch 23 and abuts against the bottom wall of the rotating ring 13, one side of the locking rod 22 is in contact with the flat part, and its bottom end is in contact with the abutting block 27. In this way, the rotation of the locking disc 20 can be restricted by the locking rod 22.When the rotating ring 13 forces the locking disc 20 and the movable rod 7 to rotate, the sleeve 4 can be moved towards the cornea synchronously through the slider 10 and the groove 9, so that the detection mechanism 2 at one end of the main body 1 is moved to a position close to the cornea. Then, the micro motor drives the rotating ring 13 to continue rotating (at this time, the wedge-shaped part 24 slides relative to the bottom wall of the rotating ring 13), so as to drive the main body 1 to move along the axial direction of the sleeve 4, thereby driving the detection mechanism 2 to contact the cornea and perform ultrasound detection on the corneal thickness and axial length (when the wedge-shaped part 24 moves relative to the position of the stop 26, the two ends of the locking rod 22 are restricted by the stop 26 and the contact block 27 respectively, so that the rotating ring 13 cannot continue to rotate, that is, the rotating ring 13 has a rotation range of less than 360 degrees); after the detection is completed After completion, the micro motor drives the rotating ring 13 to reset, thereby resetting the main body 1 until the notch 23 on the rotating ring 13 moves above the wedge-shaped part 24. At this point, under the action of the spring 25, the wedge-shaped part 24 can be driven into the notch 23, and then the movable rod 7 can be reset under the action of the torsion spring. During the ultrasound detection process, if the pressure sensing unit 3 detects that the pressure on the cornea is too high, the micro motor drives the main body 1 to move away from the cornea along the sleeve 4, thereby reducing the pressure on the cornea. If the pressure sensing unit 3 detects that the pressure on the cornea is too low, the micro motor drives the main body 1 to move slightly closer to the cornea along the sleeve 4, thereby slightly increasing the pressure on the cornea, so that the monitoring mechanism fits the cornea more closely.

[0047] In summary, when the device is in use, rotating the rotating ring 13 initially causes the two squeezing parts 5 to move away from each other, and at the same time initially drives the lead screw 15 to rotate, so that the main body 1 moves a certain distance towards the cornea along the axis of the sleeve 4. When the two squeezing parts 5 move away from each other, the sleeve 4 can also move a certain distance towards the cornea along the handle 6. In this way, the detection mechanism 2 can be moved to a position close to the cornea. Then, the rotating ring 13 continues to rotate to fine-tune the position of the detection mechanism 2 so that the detection mechanism 2 fits the cornea of ​​the examinee. After use, the rotating ring 13 resets to reset all components.

[0048] The foregoing has only described certain exemplary embodiments of the present invention by way of illustration. Undoubtedly, those skilled in the art can modify the described embodiments in various ways without departing from the spirit and scope of the present invention. Therefore, the foregoing drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. An ophthalmic A-scan ultrasound device, characterized in that, It is an ultrasonic probe, which includes a main body, on which are disposed: The detection mechanism is located at one end of the main body and is used for ultrasonic detection of corneal thickness and axial length; the detection mechanism has two squeezing parts on the side away from the main body, and when the main body is close to the cornea, the two squeezing parts move away from each other to force the upper and lower eyelids to open. A pressure sensing unit, located within the detection mechanism, is used to monitor the pressure exerted by the detection mechanism on the cornea. An adjustment mechanism is disposed on the main body and is used to adjust the pressure exerted on the cornea by the detection mechanism; the adjustment mechanism includes a sleeve, the main body is slidably connected inside the sleeve, and a linear drive assembly for driving the main body to move along the axial direction of the sleeve; The sleeve is fitted with a handle, on which two movable rods are rotatably connected. A torsion spring is provided between the movable rods and the handle. One end of the movable rod is fixed to a pressing part, and the other end is constructed with a through groove. A sliding groove is constructed on the handle. A slider is fixed to the outer wall of the sleeve, and the slider is located in both the sliding groove and the through groove. A limiting groove is constructed on the handheld part, and a limiting block is constructed on the rotating shaft of the movable rod, with the limiting block located within the limiting groove; The linear drive assembly includes a rotating ring rotatably connected to the handheld part, an internal gear constructed on the inner wall of the rotating ring, a lead screw rotatably connected to the sleeve, a first connecting part fixed on the lead screw, a second connecting part rotatably connected inside the handheld part, the second connecting part being inserted into the first connecting part, a drive gear fixed on the second connecting part, the drive gear meshing with the internal gear, and a drive block fixed on the outer wall of the main body, the drive block being threadedly connected to the lead screw; A locking mechanism is provided between the handheld part and the sleeve. After the two pressing parts move away from each other, the locking mechanism locks the relative position of the handheld part and the sleeve. The locking mechanism includes a locking disc fixed to a movable rod, the locking disc having a locking groove, a locking rod slidably connected inside the handle, a wedge-shaped portion at the top of the locking rod, a notch adapted to the wedge-shaped portion at the bottom of the rotating ring, and a spring inside the handle forcing the wedge-shaped portion into the notch. The first connecting part is a non-rotating body, and the second connecting part has a connecting groove that is adapted to the first connecting part.

2. The ophthalmic A-scan ultrasound device according to claim 1, characterized in that, The detection mechanism comprises two hydrogel layers, and the pressure sensing unit is located between the two hydrogel layers.

3. The ophthalmic A-scan ultrasound device according to claim 1, characterized in that, The outer wall of the extrusion section is constructed with an anti-slip layer.

4. The ophthalmic A-scan ultrasound device according to claim 1, characterized in that, The pivot of the movable rod and the pressing part at one end of the movable rod are located on both sides of the central axis of the main body.

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