CN117982289A - Ophthalmic surgical device - Google Patents

Abstract

The invention provides an ophthalmic surgical device comprising a handle, a piezoelectric actuator, a driving power source, a contact and a connecting rod. The handle defines a first longitudinal direction and a first longitudinal axis parallel to the first longitudinal direction. The piezoelectric actuator is disposed within the handle in a first longitudinal direction and includes a first piezoelectric actuation element that is operable to generate vibrations in a first vibration direction. The contact is used to contact a surgical site during an ophthalmic surgical procedure. The contact has a main board in a first plane and a ridge formed at an edge of the main board. The first plane is orthogonal to a longitudinal section intersecting the first longitudinal axis. The first plane and the first longitudinal direction form an included angle which is larger than zero degrees and smaller than or equal to 90 degrees. The first piezoelectric actuation element drives the contact to reciprocate between a first longitudinal position and a second longitudinal position along a first longitudinal direction in a vibration driving direction in an activated state, so that the main board reciprocates between the first longitudinal position and the second longitudinal position along a normal direction of the main board.

Description

Ophthalmic surgical device

Technical Field

The invention relates to a medical instrument, in particular to an ophthalmic surgical device.

Background

Keratoplasty is one of the effective means of treating keratopathy to restore vision. To improve the surgical effect, the corneal graft may remove only a portion of tissue replacing the cornea, such as a diseased layer of the cornea, without removing the entire cornea. Because of the thinner thickness of the various tissue layers of the cornea, surgery to remove a particular diseased layer places greater demands on accuracy, experience, and surgical instruments than to ablate the entire cornea. The tissue to be preserved may be injured by some carelessness, and even the operation may fail.

Disclosure of Invention

According to one aspect, the present invention provides an ophthalmic surgical device for corneal tissue delamination of a cornea portion of an eye. According to one embodiment. The ophthalmic surgical device of the present invention includes a handle, a piezoelectric actuator, a driving power source, a contact, and a linkage. The handle defines a first longitudinal direction and a first longitudinal axis parallel to the first longitudinal direction. The piezoelectric actuator is disposed within the handle in a first longitudinal direction and includes a first piezoelectric actuation element that is operable to generate vibrations in a first vibration direction. The contact is used to contact a surgical site during an ophthalmic surgical procedure. The contact has a main board in a first plane and a ridge formed at an edge of the main board. The first plane is orthogonal to a longitudinal section intersecting the first longitudinal axis. The first plane and the first longitudinal direction form an included angle which is larger than zero degrees and smaller than or equal to 90 degrees. The first piezoelectric actuation element drives the contact to reciprocate between a first longitudinal position and a second longitudinal position along a first longitudinal direction in an activated state along a vibration direction, so that the main board reciprocates between the first longitudinal position and the second longitudinal position along a normal direction of the main board, and partial tissues or pathological layers of the cornea of the eye are peeled off from the substrate layer or the reserved layer.

Preferably, the ridge has a blunt edge such that when the contact is displaced in a direction parallel to the first plane toward and contacts the surgical site, the ridge has a pressure to the surgical site that is less than a pressure threshold of the surgical site that resists cutting, such that the ridge does not cause the surgical site to be cut, reducing the risk of injuring the retained tissue and surrounding sites.

Alternatively, the rib has a sharp edge such that when the contact is displaced toward and contacts the surgical site in a direction parallel to the first plane, the rib has a pressure to the surgical site that is greater than a pressure of the surgical site that resists cutting, such that the rib causes the surgical site to be cut.

Preferably, the piezoelectric actuator further comprises a second piezoelectric actuation element operable to generate vibrations in a second vibration direction, the second vibration direction being orthogonal to the first vibration direction and the normal direction, the rib having a leading edge end point and defining a tangential direction intersecting the leading edge end point and parallel to the second vibration direction, wherein vibration of the second piezoelectric actuation element in the second vibration direction in an activated state drives the contact to reciprocate along the second vibration direction between a first transverse position and a second transverse position such that the rib reciprocates along the tangential direction.

Preferably, the sharp edge of the ridge is formed to face in a direction parallel to the tangential direction, wherein the reciprocal displacement of the ridge along the tangential direction is such that when the contact is displaced toward and contacts the surgical implementation site in a direction parallel to the first plane, the ridge causes the surgical implementation site to be cut in a direction parallel to the direction in which the second vibration is implemented.

Preferably, the ophthalmic surgical device according to the present invention further comprises a control switch coupled to the driving power source and the piezoelectric actuator, the control switch being configured to independently control the vibration of the first piezoelectric actuation element and the second piezoelectric actuation element in the first vibration direction and the second vibration direction, respectively.

A control switch may be provided in the handle such that the control switch may be operated during the process of the handle being held. Alternatively, a control switch may be provided between the drive power source and the handle. Or a control switch may be provided in the driving power supply.

Preferably, the connecting rod is arranged along said longitudinal section. The connecting rod comprises a first end coupled to the piezoelectric actuator, a second end coupled to the contact, and a connecting portion between the first end and the second end, wherein the connecting portion protrudes toward an opposite side of the handle with respect to the first plane.

Preferably, the connecting portion has a connecting portion curvature that is greater than a base portion curvature of a base portion profile of the surgical site.

According to another embodiment. The ophthalmic surgical device of the present invention includes a handle, a piezoelectric actuator, a drive power source electrically connected to the piezoelectric actuator, a contact, and a linkage coupled between the piezoelectric actuator and the contact. A handle for being held during an ophthalmic procedure, the handle defining a first longitudinal direction, a first longitudinal axis parallel to the first longitudinal direction, and a first transverse axis orthogonal to the first longitudinal axis. The piezoelectric actuator is disposed within the handle along the first longitudinal direction. The contact is used for contacting an operation implementation part in the ophthalmic operation process, the contact is provided with a main board in a first plane and a prismatic part formed at the edge of the main board, the longitudinal section intersecting with the first longitudinal axis is orthogonal to the first plane, and the first plane and the first longitudinal direction form an included angle which is larger than zero degrees and smaller than or equal to 90 degrees. Vibration of the piezoelectric actuator in an activated state drives the contact to reciprocate along the first transverse axis between a first transverse position and a second transverse position, so that the edge part reciprocates between the first transverse position and the second transverse position in a tangential direction orthogonal to the normal direction of the main board and parallel to the first transverse axis.

Preferably, the ridge has a sharp edge such that when the contact is displaced towards and contacts the surgical site in a direction parallel to the first plane, the ridge has a pressure to the surgical site that is greater than a pressure of the surgical site against cutting, such that the ridge causes the surgical site to be cut in a tangential direction orthogonal to a normal direction of the main plate.

Ophthalmic surgical devices according to embodiments of the present invention may be best understood and practiced by the following detailed description.

Brief description of the drawings

Fig. 1 is a schematic perspective view of an ophthalmic surgical device according to one embodiment of the present invention.

Fig. 2 is a cross-sectional perspective view of the ophthalmic surgical device shown in fig. 1 and a partial enlarged view of the contact portion.

Fig. 3 is a schematic perspective view and a partial enlarged view of the ophthalmic surgical device of fig. 1 in an applied state.

FIG. 4 is a partial front view and partial enlarged view of the ophthalmic surgical device of FIG. 3 in use;

Fig. 5 is a graph of vibration frequency versus resulting displacement of a piezoelectric actuator of the ophthalmic surgical device shown in fig. 1.

Fig. 6 is a schematic perspective view of an ophthalmic surgical device according to another embodiment of the present invention.

Fig. 7 is a cross-sectional perspective view of the ophthalmic surgical device shown in fig. 6 and a partial enlarged view of the contact portion.

Fig. 8 is a further enlarged, example perspective view of the contact portion of the ophthalmic surgical device of fig. 6.

Fig. 9 is an enlarged front view of the contact portion of the ophthalmic surgical device of fig. 6.

Detailed Description

Reference in the specification to "one embodiment," "another embodiment," or "an embodiment" (or similar descriptions) means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, appearances of the phrases "in one embodiment" or "in an embodiment" in various places throughout this specification are understood to refer to the same embodiment, or to different embodiments.

Furthermore, the described aspects, features, structures, or characteristics may be combined in any suitable manner in one or more embodiments. The following description provides specific details to provide a thorough and complete understanding of embodiments of the invention, so that those skilled in the art may understand and practice the embodiments of the invention. Thus, descriptions of some or all known structures, materials, or operations may be omitted herein.

The cornea is a multilayer transparent tissue located in the anterior part of the eyeball. Cornea implantation surgery can be one of the possible treatment options when the cornea tissue forms lesions. In order to reduce damage to corneal tissue during surgery, corneal grafting procedures may be performed to implant or replace only specific diseased layers without resecting the entire cornea. Surgery for a particular diseased layer of the cornea typically requires the use of a sharp surgical knife to cut along the stromal interface between the particular diseased layer and the other layers of corneal tissue, while maintaining the cutting trajectory of the knife within the same stromal interface as much as possible to ensure the integrity and optical smoothness of the remaining corneal tissue after the ablation procedure is completed. In this type of procedure, the depth of cut, speed, thickness of the outer layer, quality and integrity of the cut layer are largely dependent on the medical experience of the ophthalmic surgeon and the field performance of the surgical procedure. In addition, the curved morphology of the cornea increases the difficulty of the procedure since the cutting operation along the curved or curved direction is more difficult to control than the cutting operation along the straight posterior plane direction. If the corneal topography itself is not maintained within the stromal interface, the intracorneal cutting procedure will likely result in uneven stromal thickness of the remaining tissue, localized damage, larger wounds left after surgery, increased risk of localized infection, longer post-operative recovery, and/or less desirable vision recovery effects, etc.

The invention provides an ophthalmic surgical device which is used for stripping cornea part lamellar tissues to be removed from a stroma layer in a delamination mode and in a further accurate operation so as to provide a technical scheme of safely, effectively and relatively low-risk local tissue removal and delamination of cornea tissues. The ophthalmic surgical device according to the present invention may also be used in other surgical procedures such as cornea surgery, cataract surgery, glaucoma surgery, retinal surgery, and the like. In addition, the ophthalmic surgical device according to the present invention can be used for various ocular tissues for orbital and ocular plastic surgery, including surgery involving the cornea, sclera, intraocular tissue, orbital/periorbital tissues, periorbital skin, and the like.

As shown in fig. 1 to 5, the ophthalmic surgical device 100 according to one embodiment of the present invention includes a handle 110, a piezoelectric actuator 130 disposed inside the handle 110, a driving power source 150 electrically connected to the piezoelectric actuator 130, a control switch 140 coupled to the driving power source 150 and the piezoelectric actuator 130, a contact 180, and a link 160 coupled between the piezoelectric actuator 130 and the contact 180.

The handle 110 may have an elongated shape suitable for grasping by a user for performing a procedure, such as an elongated cylindrical shape as shown in fig. 1. The handle 110 defines a first longitudinal direction 112 and a first longitudinal axis 118 parallel to the first longitudinal direction 112. The piezoelectric actuator 130 includes a first piezoelectric actuation element 132 that can generate vibrations in a first vibration direction 132 a. The piezoelectric actuator 130 is disposed within the handle 110 along the first longitudinal direction 112 such that the first vibration direction 132a is parallel to the first longitudinal direction 112. The first piezoelectric actuation element 132 may be a single hollow cylinder piezoelectric actuator or an annular piezoelectric actuator as shown in fig. 1, or a piezoelectric ceramic stack actuator formed by stacking a plurality of hollow cylinder piezoelectric actuators or annular piezoelectric actuators in the axial direction, so that the piezoelectric ceramic stack actuator can amplify the displacement amplitude generated by the single piezoelectric actuator.

The contact 180 is a disc-shaped paddle made of a material capable of providing a predetermined strength and rigidity, such as stainless steel, for contacting and applying force to the site of operative application during ophthalmic surgery, i.e., assisting in delamination and stripping of corneal tissue, such as a portion of lamellar tissue of the cornea, during a keratolytic procedure. The contact 180 has a main plate 183 in a first plane 182 and a ridge 185 formed at an edge of the main plate 183. The first plane 182 is orthogonal to the longitudinal section 102 through the first longitudinal axis 132. The first plane 182 forms an angle 186 with the first longitudinal direction 112 that is greater than zero degrees and less than or equal to 90 degrees. Preferably, included angle 186 is between 30 degrees and 60 degrees.

The connecting rod 160 is fixedly connected between the piezoelectric actuator 130 and the contact 180, so that the displacement generated by the piezoelectric actuator 130 is transmitted to and drives the contact 180 to perform corresponding displacement through the connecting rod 160. The contact 180 may be fixedly connected to the link 160, such as by welding, integral swaging or insert molding. The linkage 160 may also be connected to the handle 110 and to the piezoelectric actuator 130 in a similar or other manner. The link 160 is disposed along the longitudinal section 102, i.e., the longitudinal axis 162 of the link 160 is coplanar with the longitudinal section 102. The linkage 160 includes a first end 163 coupled to the piezoelectric actuator 130, a second end 168 coupled to the contact 180, and a connection 165 between the first end 163 and the second end 168. The connection portion 165 is convex toward a side opposite to the handle 110 with respect to the first plane 182.

The longitudinal axis 162 of the link 160 may be a continuously conductive curve. The body of the link 160 may have a circular cross-section that is continuously distributed along the longitudinal axis 162. The cross-sectional area is greater proximate the first end 163 than proximate the second end 168, and the cross-sectional area of the link 160 tapers along the longitudinal axis 162 from the first end 163 to the second end 168. The longitudinal axis 162 has a joint curvature 162r. The connecting portion curvature 162r is greater than the base portion curvature of the base portion profile of the surgical site to which the ophthalmic surgical device 100 according to the embodiment of the present invention is applied. For example, the joint curvature 162r is greater than the curvature of the head contour curve 32r of the patient receiving the ophthalmic procedure, such that, in use, vibrations of the linkage 160 are not transmitted to other body parts than the site of the patient's procedure.

Actuation of the drive power supply 150 causes the first piezoelectric actuation element 132 to be in an activated state such that the first piezoelectric actuation element 132 produces vibration in a first vibration direction 132a, which in turn drives the contact 180 for a reciprocating displacement motion 180d along the first longitudinal direction 112 between a first longitudinal position 181 and a second longitudinal position 189. Because the contact 180 is disposed at an angle 186 between the first plane 182 and the first longitudinal direction 112 that is greater than zero degrees and less than or equal to 90 degrees, displacement of the contact 180 along the first longitudinal direction 112 results in a normal reciprocal displacement 182d of the main plate 182 between the first longitudinal position 181 and the second longitudinal position 189 along a normal direction 182n of the main plate 182.

The rib 185 has a blunt edge 185e, such as a smoothly rounded transition edge, such that when the contact 180 is displaced toward and contacts the surgical site in a direction parallel to the first plane 182, the pressure of the rib 185 against the surgical site is less than the threshold pressure of the corneal tissue of the surgical site against cutting, such that the rib 185 does not cause the surgical site to be cut or cut-like damaged.

In the terms "blunt edge", "blunt edge" and in contrast the terms "sharp edge", "sharp edge" refer to a blade comprising edges of a sheet-shaped instrument or component, such as an ophthalmic surgical device, a contact, a blade of a surgical instrument, etc., having the desired physical characteristics of edge structure, size, shape, material, hardness, strength, and rigidity for an object of the same material, structure, shape, and size, such as an ophthalmic cornea, such that the desired degree of edge separation of the object in a cutting manner at a predetermined operating step, operating force, pressure, and/or speed, such as a stainless steel blade, ceramic blade, sapphire blade, diamond blade, etc., for performing cutting of human tissue in an ophthalmic or other procedure. In contrast, the terms "blunt edge", "blunt edge" refer to the edge of the sheet-shaped instrument or component that is formed by the edges, is applied to the same body tissue, and does not have the sharpness required to be able to separate the object in a cutting manner at the same operating steps, operating forces, pressures and/or speeds. For example, if the thickness of each type of cutting edge is used as a measure, a "sharp-edged" cutting edge refers to a cutting edge having such a thin size that the pressure applied to the cut object at the same pressure is sufficiently large so that the pressure applied to the cut object at the same pressure is greater than the cut pressure threshold of the cut object, so that the "sharp-edged" cutting edge can enter and divide the cut object in a cutting manner without substantial damage or destruction of a predetermined portion around the incision through which the cutting edge passes and the tissue cut north, but at the same time, substantial damage or destruction of an unintended portion around the incision may occur due to movement of the blade toward an unintended position. In contrast, a "blunt edge" edge means that the thickness of such edge is greater than the thickness of a "sharp edge" edge, i.e., the "blunt edge" edge has such a thick dimension that the pressure acting on the object to be cut is less than the cut pressure threshold of the object to be cut at the same pressure, i.e., the "blunt edge" and "blunt edge" are not able to enter and divide the object to be cut in a cutting manner at the same pressure. At the same time, the contact of the 'blunt edge' cutting edge, even if moving towards the non-predetermined position, will not cause substantial damage or destruction to the stressed or surrounding non-predetermined location.

In practice, the ophthalmic surgical device 100 according to the present example is used for a peeling operation of lamellar tissue of a cornea portion of an eye. As shown in fig. 3 and 4, the contact 180 of the ophthalmic surgical device 100 is positioned between the starting positions of the layer to be peeled 58 and the retention layer 52 of the cornea 50 of the eye such that the first plane 182 in which the contact 180 lies is parallel to the interface 55 between the layer to be peeled 58 and the retention layer 52. In the activated state of the driving power source 150, the first piezoelectric actuation element 132 is activated, generating vibrations in the first vibration direction 132a, i.e. parallel to the first longitudinal direction 112. Vibration of the first piezoelectric designating element 132 is transmitted to the contact 180 through the handle 110 and the link 160, and drives the contact 180 to reciprocate 180d along the first longitudinal direction 112.

The distance of the reciprocating displacement movement 180d of the contact 180 in the first longitudinal direction 112 varies with the output voltage and frequency of the drive power supply 150. As shown in fig. 5, according to one specific example, the ophthalmic surgical device 100 of the present embodiment can generate a displacement maximum of about 50 micrometers for the first piezoelectric actuator 132 when the peak-to-peak voltage value output by the driving power source 150 is 20Vpp and the frequency is 22 khz. According to another embodiment, the ophthalmic surgical device 100 of the present embodiment can cause the contact 180 to reciprocate more than 10 microns in travel along the first longitudinal direction 112 when the first piezoelectric actuation element 132 receives 2 watts of input power, a vibration frequency of 20khz to 30 khz, and a voltage peak to peak of 400Vpp, and the maximum temperature generated by the contact 180 during operation is below 40 degrees celsius.

The reciprocating displacement movement 180d of the contact 180 along the first longitudinal direction 112 causes the main plate 182 to undergo a normal reciprocating displacement 182d along the normal direction 182n of the main plate 182 at the same vibration frequency as the first piezoelectric actuation element 132 between the first longitudinal position 181 and the second longitudinal position 189.

Because the contact 180 is disposed between the to-be-peeled layer 58 of the cornea 50 and the initial position of the retention layer 52, the main board 182 reciprocates 182d along the normal direction 182n of the main board 182 to drive the to-be-peeled layer 58 in contact with the contact 180 to generate corresponding high-frequency vibration, and the to-be-peeled layer 58 is applied with a force separating from the retention layer 52, so that the to-be-peeled layer 58 is promoted to be peeled from the retention layer 52.

Further, as the ophthalmic surgical device 100 advances under the direction of the operator toward the contact 180, the edge 185 of the contact 180 advances along the interface of the layer to be peeled 58 and the retention layer 52 toward the site that has not yet been peeled. The reciprocating displacement of the contact 180 in the first longitudinal direction 112 driven by the first piezoelectric actuation element 132 causes the reciprocating displacement of the main board 182 in the main board normal direction 182n to cause the peeling of the layer 58 to be peeled off from the retention layer 52 toward the portion not peeled off. At the same time, the contact 180 is driven by the first piezoelectric actuating element 132 to reciprocate 180d along the first longitudinal direction 112 to drive the ridge 185 to perform high-frequency impact on the joint interface between the layer 58 to be peeled and the retention layer 52 at the tangential plane displacement component 182t perpendicular to the normal direction 182n, thereby simultaneously promoting the layer 58 to be peeled from the retention layer 52.

In this embodiment, the edge portion 185 is a cutting edge with a blunt edge, and does not generate a cutting action on the layer to be peeled 58 or the layer to be held 52 during the advancing process towards the joint interface between the layer to be peeled 58 and the layer to be held 52, but only slides the edge portion 185 and the main board 182 along the space between the layer to be peeled 58 and the layer to be held 52, so that the layer to be peeled 58 is peeled from the layer to be held 52 under the condition of keeping the layer to be peeled 58 and the layer to be held 52 intact, or at least far below the damage probability that may be caused by cutting and separating the layer to be peeled 58 and the layer to be held 52 with a sharp-edge scalpel using the conventional technology.

According to another embodiment, as shown in fig. 6 to 9, the ophthalmic surgical device 200 of the present invention includes a handle 210, a piezoelectric actuator 230 disposed inside the handle 210, a driving power source 250 electrically connected to the piezoelectric actuator 230, a contact 280, and a link 260 coupled between the piezoelectric actuator 230 and the contact 280.

The handle 210 may have an elongated shape suitable for grasping by a user for performing a procedure, such as an elongated cylindrical shape as shown in fig. 6. The handle 210 defines a first longitudinal direction 212, a first transverse direction 214, and a first longitudinal axis 218 parallel to the first longitudinal direction 212. The piezoelectric actuator 230 includes one or more first piezoelectric actuation elements 232 that can generate vibrations in a first vibration direction 232a and one or more second piezoelectric actuation elements 234 that can generate vibrations in a second vibration direction 234a, the second vibration direction 234a being orthogonal to the first vibration direction 232 a. The piezoelectric actuator 230 is disposed within the handle 210 along the first longitudinal direction 212 such that the first vibration direction 232a is parallel to the first longitudinal direction 212 and the second vibration direction 234a is orthogonal to the first longitudinal direction 212, e.g., the first longitudinal direction 212 is a direction parallel to the first longitudinal axis 218 as shown in fig. 6.

The first piezoelectric actuating element 232 and the second piezoelectric actuating element 234 may be a single hollow cylinder piezoelectric actuator or an annular piezoelectric actuator as shown in fig. 7, or a piezoelectric ceramic laminated actuator formed by stacking a plurality of hollow cylinder piezoelectric actuators or annular piezoelectric actuators in the axial direction.

Contact 280 is a blade having rounded corners for contacting and cutting the surgical site during ophthalmic surgery, i.e., to assist in delamination of corneal tissue during keratolytic surgery. The contact 280 has a main plate 283 in a first plane 282 and a ridge 285 formed at an edge of the main plate 283. The first plane 282 is orthogonal to the longitudinal section 202 where the first longitudinal axis 232 intersects. The first plane 282 forms an angle 286 with the first longitudinal direction 212 that is greater than zero degrees and less than or equal to 90 degrees.

The connecting rod 260 is fixedly connected between the piezoelectric actuator 230 and the contact 280, so that the displacement generated by the piezoelectric actuator 230 is transmitted to the contact 280 through the connecting rod 260 and drives the contact 280 to perform corresponding displacement. The contact 280 may be fixedly connected to the link 260, such as by bolts, jackscrews 267, or the like, to form a removable fixed connection, such that the contact 280 may be replaced. The link 260 and the handle 210 and the piezoelectric actuator 230 may also be interconnected in a similar or other manner.

The ophthalmic surgical device 200 may also include a control switch 240 coupled to the drive power supply 250 and the piezoelectric actuator 230. The control switch 240 is configured to independently control the vibration of the first piezoelectric actuation element 232 and the second piezoelectric actuation element 234 in the first vibration direction 232a and the second vibration direction 234a, respectively. The control switch 240 may be provided in the handle 210 to facilitate the user to operate the control switch 240 through the handle 210 while holding the handle 210 and performing the operation. Alternatively, the control switch 240 may be provided in the driving power source 250 to simplify the operation of the user holding the handle 210 for surgery. Alternatively, the control switch 240 may be disposed between the driving power source 250 and the handle 210 independently, for example, at a position that is convenient to control by manual control or foot control, so that the driving power source 250 and the handle 210 can be operated conveniently and efficiently, and the structure and manufacturing can be standardized, which is helpful for mass manufacturing.

Actuation of the drive power supply 250 causes the first piezoelectric actuation element 232 to be in an activated state such that the first piezoelectric actuation element 232 produces vibration in a first vibration direction 232a, which in turn drives the contact 280 for reciprocal displacement along the first longitudinal direction 212 between a first longitudinal position 281 and a second longitudinal position 289. Because the contact 280 is disposed at an angle 286 between the first plane 282 and the first longitudinal direction 212 that is greater than zero degrees and less than or equal to 90 degrees, displacement of the contact 280 along the first longitudinal direction 212 results in a reciprocal displacement 282d of the main plate 283 between the first longitudinal position 281 and the second longitudinal position 289 along a normal direction 282n of the main plate 283.

Under the control of the control switch 240, the driving power source 250 may further cause the second piezoelectric actuation element 234 to be activated simultaneously, independently or alternately with the first piezoelectric actuation element 232, such that the second piezoelectric actuation element 234 generates vibration along the second vibration direction 234a, and subsequently drives the contact 280 to perform a tangential reciprocating displacement 282e along the first lateral direction 214 between the first lateral position 283 and the second lateral position 287.

The rib 285 has a sharp edge 285e such that when the contact 280 is displaced toward and contacts the surgical site in a direction parallel to the first plane 282, the rib 285 has a pressure to the surgical site that is greater than a pressure threshold of the surgical site that resists cutting, such that the rib 285 may cause the surgical site to be cut.

The ridge 285 has a tangential direction 285t intersecting the leading edge point and parallel to the second vibration direction 234 a. The vibration driving contact 280 of the second piezoelectric actuator 234 in the second vibration direction 234a is reciprocally displaced between the first lateral position 283 and the second lateral position 287 along the second vibration direction 234a in the activated state, so that the ridge 285 makes a tangential reciprocal displacement 282e along the tangential direction 285t.

The tangential reciprocating displacement 282e of the ridge 285 in the tangential direction 285t can be set to a high frequency micro-amplitude displacement, for example, a reciprocating displacement with a vibration frequency of 20 khz to 30 khz and a stroke of between 10 micrometers and 50 micrometers, by the drive power supply 250. Compared to conventional direct push type cutting blades, the ophthalmic surgical device 200 according to the present example, which can perform high frequency micro-amplitude tangential displacement, can improve the cutting control, fine tuning ability, hand feeling and surgical accuracy of the edge 285 having a sharp cutting edge to the surgical site during the surgical procedure. Simultaneously or alternatively, displacement of the contact 280 in the first longitudinal direction 212 under the driving action of the first piezoelectric actuation element 232 brings the main plate 283 to reciprocate 282d between the first longitudinal position 281 and the second longitudinal position 289 along a normal direction 282n of the main plate 283. Accordingly, in an application of the cornea local tissue delamination surgery, the ophthalmic surgical device 200 according to the present example cuts the surgical site at the edge 285, and the normal reciprocal displacement 282d of the main plate 283 along the normal direction 282n may generate tissue to be separated by cutting, for example, the cornea lesion layer is peeled off from the remaining layer while cutting.

According to yet another embodiment, the piezoelectric actuator in the ophthalmic surgical device of the present invention may be a piezoelectric actuator that provides only lateral direction vibrations. The piezoelectric actuator vibrates in an activated state, and drives the contact to reciprocate between a first transverse position and a second transverse position along a first transverse axis, so that the edge part of the contact reciprocates between the first transverse position and the second transverse position along a direction orthogonal to the normal direction of a main board of the contact and parallel to the first transverse axis, and the contact with a sharp cutting edge can only perform high-frequency micro-amplitude tangential displacement and is used for occasions needing precise cutting operations.

The description of the various embodiments of the present invention hereinabove with reference to the accompanying drawings is to be understood as being exemplary, and not as being limiting or exhaustive. Numerous other variations, modifications, rearrangements and/or substitutions may be effected by those skilled in the art without departing from the spirit and scope of the invention.

Claims (14)

1. An ophthalmic surgical device, the ophthalmic surgical device comprising:

A handle for being held during an ophthalmic procedure, the handle defining a first longitudinal direction and a first longitudinal axis parallel to the first longitudinal direction;

A piezoelectric actuator disposed within the handle along the first longitudinal direction, the piezoelectric actuator including a first piezoelectric actuation element operable to generate vibrations along a first vibration direction;

a driving power source electrically connected to the piezoelectric actuator;

The contact is used for contacting an operation implementation part in the ophthalmic operation process, and is provided with a main plate in a first plane and a prismatic part formed at the edge of the main plate, wherein the longitudinal section of the first plane intersecting with the first longitudinal axis is orthogonal, and an included angle between the first plane and the first longitudinal direction is larger than zero degrees and smaller than or equal to 90 degrees; and

A linkage coupled between the piezoelectric actuator and the contact,

Wherein vibration of the first piezoelectric actuation element in the first vibration direction in an activated state drives the contact to reciprocate between a first longitudinal position and a second longitudinal position along the first longitudinal direction, so that the main plate reciprocates between the first longitudinal position and the second longitudinal position along a normal direction of the main plate.

2. The ophthalmic surgical device of claim 1, wherein the rib has a blunt edge such that when the contact is displaced toward and contacts a surgical site in a direction parallel to the first plane, the rib has a pressure to the surgical site that is less than a pressure threshold of the surgical site that resists cutting, such that the rib does not cause the surgical site to be cut.

3. The ophthalmic surgical device of claim 1, wherein the rib has a sharp edge such that when the contact is displaced toward and contacts a surgical site in a direction parallel to the first plane, the rib has a pressure to the surgical site that is greater than a pressure of the surgical site that resists cutting, such that the rib causes the surgical site to be cut.

4. The ophthalmic surgical device of claim 3, wherein the piezoelectric actuator further comprises a second piezoelectric actuation element operable to generate vibration in a second vibration direction, the second vibration direction being orthogonal to the first vibration direction and the normal direction, the rib having a leading edge endpoint and defining a tangential direction intersecting the leading edge endpoint and parallel to the second vibration direction, wherein vibration of the second piezoelectric actuation element in the second vibration direction in an activated state drives reciprocal displacement of the contact in the second vibration direction between a first lateral position and a second lateral position such that the rib is reciprocally displaced in the tangential direction.

5. The ophthalmic surgical device of claim 4, wherein the sharp edge of the rib is formed to face in a direction parallel to the tangential direction, wherein reciprocal displacement of the rib along the tangential direction causes the surgical application site to be cut in a direction parallel to the direction of application of the second vibration when the contact is displaced toward and contacts the surgical application site in a direction parallel to the first plane.

6. The ophthalmic surgical device of claim 4, further comprising a control switch coupled to the drive power source and the piezoelectric actuator, the control switch configured to independently control vibration of the first piezoelectric actuation element and the second piezoelectric actuation element in the first vibration direction and the second vibration direction, respectively.

7. The ophthalmic surgical device of claim 6, wherein the control switch is disposed in the handle such that the control switch can be operated during the process of the handle being held.

8. The ophthalmic surgical device of claim 6, wherein the control switch is disposed in the drive power supply.

9. The ophthalmic surgical device of claim 6, wherein the control switch is disposed between the drive power source and the handle.

10. The ophthalmic surgical device of claim 1, wherein the links are disposed along the longitudinal section.

11. The ophthalmic surgical device of claim 10, wherein the linkage comprises a first end coupled to the piezoelectric actuator, a second end coupled to the contact, and a connection between the first end and the second end, wherein the connection is convex toward an opposite side of the handle with respect to the first plane.

12. The ophthalmic surgical device of claim 11, wherein the connecting portion has a connecting portion curvature that is greater than a base portion curvature of a base portion profile of the surgical site.

13. An ophthalmic surgical device, the device comprising:

A handle for being held during an ophthalmic procedure, the handle defining a first longitudinal direction, a first longitudinal axis parallel to the first longitudinal direction, and a first transverse axis orthogonal to the first longitudinal axis;

A piezoelectric actuator disposed within the handle along the first longitudinal direction;

a driving power source electrically connected to the piezoelectric actuator;

The contact is used for contacting an operation implementation part in the ophthalmic operation process, and is provided with a main plate in a first plane and a prismatic part formed at the edge of the main plate, wherein the longitudinal section of the first plane intersecting with the first longitudinal axis is orthogonal, and an included angle between the first plane and the first longitudinal direction is larger than zero degrees and smaller than or equal to 90 degrees; and

A linkage coupled between the piezoelectric actuator and the contact,

The vibration of the piezoelectric actuator in an activated state drives the contact to reciprocate along the first transverse axis between a first transverse position and a second transverse position, so that the edge part reciprocates between the first transverse position and the second transverse position in a tangential direction orthogonal to the normal direction of the main board and parallel to the first transverse axis.

14. The ophthalmic surgical device of claim 13, wherein the rib has a sharp edge such that when the contact is displaced toward and contacts a surgical site in a direction parallel to the first plane, the rib has a pressure to the surgical site that is greater than a pressure of the surgical site that resists cutting, such that the rib causes the surgical site to be cut in a tangential direction that is orthogonal to a normal direction of the main plate.