CN215651502U - Bone tissue ablation device and equipment - Google Patents

Abstract

The utility model provides a bone tissue ablation device and equipment, relates to the technical field of medical instruments, and aims to solve the problem that an electric drill or an electric saw is easy to cause mechanical damage to bone tissue during an operation in the related art. The bone tissue ablation device includes: a housing having a laser chamber and a suction chamber; the shell is sequentially provided with a laser inlet, a collimation element, a focusing element and a laser outlet, and the collimation element is configured to modulate laser emitted from the laser inlet into parallel laser; the focusing element is configured to focus the parallel laser light emitted from the collimating element at a first focal point; the shell is also provided with a suction port, and the suction port is configured to suck the air outside the shell into the suction chamber along the suction direction of the suction port; the optical axis of the focusing element is perpendicular to a first plane where the first focus is located, and the part of the air suction port extending to the first plane along the air suction direction covers the first focus. The utility model is suitable for grinding and cutting bone tissues.

Description

Bone tissue ablation device and equipment

Technical Field

The utility model relates to the technical field of medical equipment, in particular to a bone tissue ablation device and equipment.

Background

Bone tissue generally refers to hard connective tissue, the composition of which generally includes calcium-phosphate rock material. For example, hydroxyapatite is a main inorganic component constituting bones and teeth, and when bone tissues are diseased, the hydroxyapatite in the diseased region is often cut out.

In the case of a living body (e.g., a human body) having the above-mentioned bone tissue, it is common in the related art to cut a portion to be cut off by using an electric drill or an electric saw. This is usually done when the bone tissue is detached from the body or in vivo but with a better field of view and a larger working space, and if the bone is abraded directly in vivo without the surgical conditions, the surgical procedure will fail. In addition, the mode of electric drilling or electric sawing is difficult to control the accurate position of the part to be cut during operation well, and the adjacent soft tissue is easy to be accidentally injured; meanwhile, the electric drill and the electric saw generate vibration in the working process, and the action area of the electric drill and the electric saw is large, so that mechanical damage is easily caused to bone tissues, and the operation effect is influenced.

Disclosure of Invention

The utility model aims to provide a bone tissue ablation device and equipment, which are used for solving the problems that an electric drill or an electric saw in the related art is easy to cause mechanical damage to bone tissue during operation.

In order to achieve the above purpose, the utility model provides the following technical scheme:

a bone tissue ablation device comprising: a housing having a laser chamber and a suction chamber; the laser cavity is internally provided with a laser inlet and a laser outlet, a collimating element and a focusing element are sequentially arranged between the laser inlet and the laser outlet, and the collimating element is configured as follows: modulating laser light injected from the laser inlet into parallel laser light; the focusing element is configured to: focusing the parallel laser light emitted from the collimating element to a first focal point; the housing is further provided with a suction opening, and the suction opening is configured to: sucking the air outside the housing into the suction chamber along the suction direction of the suction port; the optical axis of the focusing element is perpendicular to a first plane where the first focus is located, and the part of the air suction port extending to the first plane along the air suction direction covers the first focus.

In some embodiments, a portion of the suction port extending to the first plane in the suction direction is a suction coverage surface, and the first focus is located in the suction coverage surface.

In some embodiments, the air suction covering surface is a circular covering surface, the circle center of the circular covering surface coincides with the first focus, and the diameter of the circular covering surface is 3-4 mm.

In some embodiments, a portion of the suction port extending to the first plane in the suction direction is a second focal point, and the second focal point coincides with the first focal point.

In some embodiments, the suction chamber surrounds the laser chamber; and/or the air suction port is arranged around the laser outlet.

In some embodiments, the housing comprises a first housing, a second housing and a third housing detachably connected in sequence; the laser inlet is arranged at one end, far away from the second shell, of the first shell; the first housing and the second housing are connected to form a first accommodating cavity which can accommodate the collimating element, and the shape and the size of the first accommodating cavity are matched with those of the collimating element; be equipped with fixed cover in the third casing, be equipped with in the fixed cover and be used for holding focusing element's second holds the chamber, fixed cover one end still is equipped with and is used for the restriction the locating part of focusing element activity, the locating part with fixed cover can dismantle the connection.

In some embodiments, an air outlet is provided on the second housing, and the second housing has a first suction chamber, the third housing has a second suction chamber, the second suction chamber is in communication with the suction port; and a sealing element is arranged at the joint between the second shell and the third shell.

In some embodiments, the laser inlet is a carbon dioxide laser inlet or an erbium laser inlet.

The utility model also provides bone tissue ablation equipment which comprises the bone tissue ablation device according to the embodiments, and further comprises a laser and negative pressure supply device, wherein the laser and negative pressure supply device is provided with a laser interface and a trachea interface, the laser interface is connected with a laser inlet of the bone tissue ablation device through an optical fiber, and the trachea interface is connected with an air outlet of the bone tissue ablation device through a trachea.

In some embodiments, the optical fiber is an armored optical fiber; the air pipe is a high-pressure machine air pipe.

The bone tissue ablation device provided by the utility model at least has the following beneficial effects:

utilize laser to melt bone tissue to can realize bone tissue's cutting, also can increase the operation field of vision simultaneously, effectively avoid the operation in-process to the mechanical damage that causes around the bone tissue, alleviate the operation operator because the physical demands that mechanical vibration brought, reduce the probability to the soft tissue formation accidental injury that closes on, the wound that causes when reducing the bone tissue cuts, thereby be favorable to postoperative bone tissue's restoration. In addition, the air suction port can be used for well clearing debris generated in the process of cutting the bone tissue, so that the part needing to be cut off subsequently can be more clearly exposed, and the process of the subsequent operation is facilitated; but also can take away the heat generated by cutting the bone tissue in time, thereby being beneficial to avoiding the heat damage of the part of heat to the bone tissue. The utility model is suitable for grinding and cutting bone tissues.

Drawings

In order to more clearly illustrate the technical solution of the present invention, the drawings needed to be used in some embodiments of the present invention will be briefly described below, and it is apparent that the drawings in the following description are only drawings of some embodiments of the present invention, and it is obvious for those skilled in the art that other drawings can be obtained according to the drawings. Furthermore, the drawings in the following description may be regarded as schematic diagrams, and do not limit the actual size and the like of products related to the embodiments of the present invention.

Fig. 1 is a schematic cross-sectional view of a bone tissue ablation device according to some embodiments;

fig. 2 is an operational schematic diagram of a partial structure of a bone tissue ablation device according to some embodiments;

fig. 3 is an operational schematic diagram of a partial structure of another bone tissue ablation device according to some embodiments;

FIG. 4 is an operational schematic diagram of a partial structure of yet another bone tissue ablation device according to some embodiments;

fig. 5 is an operational schematic diagram of a partial structure of yet another bone tissue ablation device according to some embodiments;

fig. 6 is a schematic illustration of a bone tissue ablation device of fig. 1 in a disassembled configuration;

fig. 7 is a schematic structural diagram of a bone tissue ablation device according to some embodiments;

reference numerals:

1-bone tissue ablation device, 10-shell, 11-laser inlet, 12-collimation element, 13-focusing element, 14-laser outlet, 15-air suction port, 16-air outlet, 100-laser chamber, 101-first shell, 102-second shell, 103-third shell, 200-suction chamber, 1031-fixing sleeve, 1032-limiting piece, 2-laser and negative pressure supply device, 3-optical fiber and 4-trachea.

Detailed Description

The technical solutions in some embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments provided by the present invention belong to the protection scope of the present invention.

Throughout the specification and claims, the term "comprising" is to be interpreted in an open, inclusive sense, i.e., as "including, but not limited to," unless the context requires otherwise. In the description herein, the terms "some embodiments," "some examples," or "exemplary" etc. are intended to indicate that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the utility model. The schematic representations of the above terms are not necessarily referring to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be included in any suitable manner in any one or more embodiments or examples.

In the following, the terms "first", "second" are used for descriptive purposes only and are not to be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of the embodiments of the present invention, "a plurality" means two or more unless otherwise specified.

"A, and/or, B" includes the following three combinations: a alone, B alone, and a combination of A and B.

Referring to fig. 1-6, some embodiments of the present invention provide a bone tissue ablation device 1, the bone tissue ablation device 1 including a housing 10. The housing 10 has a laser chamber 100, the housing 10 is provided with a laser inlet 11 and a laser outlet 14, a collimating element 12 and a focusing element 13 are further sequentially disposed in the laser chamber 100 and between the laser inlet 11 and the laser outlet 14, and the collimating element 12 and the focusing element 13 are coaxially disposed on an optical axis. The collimating element 12 is configured to: modulating the laser light incident from the laser inlet 11 into parallel laser light; the focusing element 13 is configured to: the parallel laser light emitted from the collimating element 12 is focused on the first focal point M.

The collimating element 12 is, for example, a collimating lens or a collimating lens group; the focusing element 13 is, for example, a focusing lens or a focusing lens group.

The housing 10 further has a suction chamber 200, the housing 10 is provided with a suction opening 15, the suction opening 15 is configured to: sucking the air outside the casing 10 into the suction chamber 200 in the suction direction of the suction port 15; wherein the optical axis of the focusing element 13 is perpendicular to the first plane P where the first focus M is located, and the portion of the suction port 15 extending to the first plane P in the suction direction covers the first focus M.

The portion of the suction port 15 extending to the first plane P in the suction direction is the suction range of the suction port 15 located in the first plane P. The utility model utilizes the collimation element 12 and the focusing element 13 to modulate the laser and focus the laser on the first focus M, thereby cutting the bone tissue part to be operated at a fixed point. Since the suction range of the suction port 15 covers the position of the first focus M, debris generated during the cutting process of the bone tissue by the laser can be absorbed through the suction port 15, thereby facilitating the cutting process of the bone tissue.

On one hand, when the bone tissue ablation device 1 provided by the utility model is used for cutting by using laser, a contact type operation can be converted into a non-contact type operation, the bone tissue is ablated by using the laser, so that the bone tissue is cut, meanwhile, the operation visual field can be increased, and the success rate of the operation is improved. In addition, the laser cutting does not generate vibration during working, so that mechanical damage to surrounding bone tissues can be effectively avoided, physical consumption of an operator due to mechanical vibration can be reduced, and the operator can focus more on accurately cutting the part to be cut in the bone tissues; because the operator can not be influenced by vibration when using the bone tissue ablation device, the control effect of the operator on the device can be improved, and the probability of accidental injury to adjacent soft tissues is reduced. In addition, the laser also has certain hemostatic function and aseptic characteristic, and has smaller wound when cutting the bone tissue, thereby being beneficial to the repair of the bone tissue after the operation.

On the other hand, since the laser is easy to generate more carbonized crystal debris and hydroxyapatite microcrystal debris during the process of cutting the bone tissue, the debris can be accumulated around the cut part of the bone tissue, so that the part needing to be cut subsequently is difficult to be clearly exposed, thereby influencing the subsequent operation process. Meanwhile, the chips also accumulate more heat during the cutting process, and the heat accumulated at the bone tissue position is easy to cause thermal damage to the bone tissue, thereby affecting the repair of the bone tissue after the operation. The bone tissue ablation device provided by the utility model can well remove the debris generated in the cutting process of the bone tissue by using the air suction port 15 and the suction cavity 200, so that the part needing to be cut off subsequently can be more clearly exposed, and the process of the subsequent operation is facilitated; meanwhile, the heat generated by cutting the bone tissue can be taken away in time, so that the heat damage to the bone tissue caused by the part of heat can be avoided. Since the suction range of the suction port 15 covers the position of the first focus M, the debris can be effectively absorbed, and the absorption effect is improved.

Note that the suction direction of the suction port 15 is related to the shape of the inner wall of the casing 10 at the position of the suction passage.

In some examples, the inner walls of the casing 10 at the position of the air suction passage are all smoothly arranged, and at this time, the air suction direction of the air suction port 15 is consistent with the extending direction of the inner walls of the casing 10 around the air suction passage along the length direction of the casing 10. That is, the portion of the suction port 15 extending to the first plane P in the suction direction is the range in which the inner wall of the casing 10 around the suction passage at the position of the suction port 15 extends to the first plane P.

Illustratively, as shown in fig. 1 and 2, when the suction port 15 is provided around the laser outlet 14, the suction direction of the suction port 15 is related to the outer wall of the housing 10 at the position of the laser outlet 14 and the inner wall of the housing 10 at the position of the suction port 15. The cross section of the casing 10 at the end of the air inlet 15 may be in a ring shape such as a "loop" shape or a circular shape. For example, when the laser outlet 14 and the air inlet 15 are both circular in cross section, the housing 10 has a circular cross section at one end of the air inlet 15.

In this case, the shape of the portion of the suction port 15 extending to the first plane P in the suction direction may be the same as the sectional shape of the casing 10 at the end of the suction port 15. For example, the shape of the portion of the suction port 15 extending to the first plane P in the suction direction may be circular. And the corresponding annular region (i.e., the portion between the inner circle and the outer circle) is the suction range of the suction port 15. At this time, the inclination angle of the outer wall of the housing 10 at the position of the laser outlet 14 and the inclination angle of the inner wall of the housing 10 at the position of the air inlet 15 are adjusted, that is, the position and size of the annular region can be adjusted, so that the first focal point M is located in the annular region, and therefore, debris generated by bone tissue at the position of the first focal point M (i.e., the position cut by the laser) can be sucked away by the air inlet 15 at the first time, thereby facilitating subsequent bone tissue cutting.

Further, the shape of the portion of the suction port 15 extending to the first plane P in the suction direction may be, for example, circular. In this case, the inner wall of the housing 10 at the position of the suction port 15 extends into the first plane P and forms a circular area, while the outer wall of the housing 10 at the position of the laser exit port 14 can be realized in the following manner. Illustratively, the outer wall of the housing 10 at the position of the laser outlet 14 extends to intersect with the first focal point M in the first plane P, and the range in which the air suction port 15 can suck air is a circular area with the first focal point M as the center, at this time, the air suction port 15 has a good air suction effect at the position of the first focal point M, so that debris generated by bone tissue at the position of the first focal point M (i.e. the position cut by the laser) can be sucked away by the air suction port 15 at the first time. Further illustratively, when the outer wall of the housing 10 at the position of the laser outlet 14 extends to intersect at a position between the first plane P and the suction port 15, the suction range of the suction port 15 can be a circular region.

The size of the circular area can be adjusted by adjusting the inclination of the inner wall of the casing 10 at the position of the suction port 15.

In some examples, the circular area has a diameter of 3-4 mm. For example, the diameter of the circular area may be 3mm, 3.2mm, 3.5mm, 3.8mm, or 4mm, etc.

When a certain suction strength is applied to the air inlet 15, the smaller the suction range of the air inlet 15 is, the greater the suction strength in that range, and the better the suction effect can be achieved. When the circular area is set to the above size, a more desirable chip absorbing effect can be achieved.

Of course, the circular area may be formed in other closed shapes by adjusting the inner wall of the casing 10 at the position of the air inlet 15, and is not limited herein.

It should be noted that the references to "inner wall" and "outer wall" herein are merely for the purpose of describing the relationship of the sidewall with respect to the optical axis of the focusing element 13, and do not limit the specific positional relationship. In addition, the "cross section" may refer to a plane perpendicular to the longitudinal direction of the housing 10, i.e., the direction in which the optical axes of the collimating element 12 and the focusing element 13 are located.

Further exemplarily, as shown in fig. 3 and 4, when the suction port 15 is disposed side by side with the laser light outlet 14, at this time, the suction direction of the suction port 15 is related to the inner wall of the housing 10 at the position of the suction port 15. The sectional shape of the casing 10 at the position of the air inlet 15 is made to conform to the shape of the air inlet 15. For example, the shape of the air inlet 15 may be an ellipse, a circle, a closed polygon, or the like.

In this case, the shape of the portion of the suction port 15 extending to the first plane P in the suction direction can be kept uniform. As shown in fig. 3, the portion of the air inlet 15 extending to the first plane P in the air intake direction has an elliptical shape, and correspondingly, the elliptical area is the air intake range of the air inlet 15. As shown in fig. 4, the shape of the portion of the air inlet 15 extending to the first plane P in the air intake direction is a quadrangle, and correspondingly, the quadrangle region is the air intake range of the air inlet 15.

The size of the suction range of the suction port 15 can be adjusted by the inner wall of the casing 10 at the position of the suction port 15. As shown in fig. 3, when the extending directions of the inner walls of the casing 10 at the positions of the air inlets 15 are all kept the same, the size of the portion of the air inlets 15 extending to the first plane P in the air intake direction is kept the same as the size of the air inlets 15. As shown in fig. 4, the inner wall of the casing 10 at the position of the air inlet 15 on the side away from the optical axis of the focusing element 13 is inclined to the side away from the optical axis, so that the air suction range of the air inlet 15 can be expanded to the side away from the first focal point M, thereby expanding the air suction range of the air inlet 15. Of course, the inner wall of the casing 10 at the position of the air inlet 15 may be adjusted in other ways to adjust the air suction range of the air inlet 15, as long as it can cover the first focus M, and the utility model is not limited thereto.

In the case where the suction port 15 is provided in parallel with the laser exit 14, a plurality of sets of the suction ports 15 may be provided, and any one set of the suction ports 15 may be provided in parallel with the laser exit 14. In this case, illustratively, one suction chamber 200 is provided for each set of suction ports 15. As shown in fig. 5, 2 sets of suction ports 15 may be provided, 2 sets of suction ports 15 are located on both sides of the laser outlet 14, and the pumping chamber 200 is also correspondingly provided with 2 sets and located on both sides of the laser chamber 100. Of course, the sets of suction ports 15 may also be evenly distributed around the laser outlet 14.

In some examples, a portion of the suction port 15 extending to the first plane P in the suction direction is a suction coverage surface including the above-described annular region, circular region, elliptical region, quadrangular region, and the like, and the first focal point M is located within the suction coverage surface. Of course, the suction covering surface is not limited to the above cases, and the range extending from the suction port 15 to the first plane P in the suction direction is planar, and is included in the scope of the present invention.

In other examples, the portion of the suction port 15 extending to the first plane P in the suction direction is a second focal point, which coincides with the first focal point M. As shown in fig. 5, the portion of the air suction port 15 extending to the first plane P along the air suction direction just converges to the first focal point M, so that the air suction action point of the air suction port 15 is confocal with the working point of the laser, and therefore, the debris generated by the bone tissue at the point can be strongly adsorbed into the suction chamber 200 by the air suction port 15, and meanwhile, the bone tissue at the portion not required to be cut cannot be affected due to the large air suction range. Thereby improving the operation effect of cutting the bone tissue.

It should be noted that fig. 2 to 5 each show only a schematic view of a part of the structure of the bone tissue ablation device 1 in different embodiments. The dashed arrowed line between the collimating element 12 and the focusing element 13 illustrates the path of the laser light in the laser chamber 100, while the dashed arrowed line from the focusing element 13 to point M is also the path of the laser light after passing through the focusing element 13. In addition, the solid line with arrows starting from the first plane and entering the pumping chamber 200 represents the route of the gas pumping. The thickness of the housing 10 is not shown, but it does not limit the actual shape and size of the housing.

In some embodiments, the suction chamber 200 surrounds the laser chamber 100, the suction chamber 200 being isolated by the housing 10 at the periphery of the laser chamber 100. Thus, the suction chamber 200 has a larger buffer space, and the outer shell of the bone tissue ablation device 1 is cylindrical or truncated cone-shaped, so that the bone tissue ablation device 1 can be held by an operator.

In some embodiments, referring to fig. 1 and 6, the housing 10 includes a first housing 101, a second housing 102, and a third housing 103 detachably connected in this order; the laser inlet 11 is disposed at an end of the first housing 101 away from the second housing 102, and the laser inlet 11 is configured to: and accessing the optical fiber for transmitting the laser, and transmitting the laser in the optical fiber into the laser chamber. The optical fiber may be directly fixed at the laser inlet 11, or may be detachably fixed at the laser inlet 11, as long as it can stably transmit the laser light to the collimating element 12 after being fixed at the laser inlet 11.

The first housing 101 is connected with the second housing 102 to form a first accommodating cavity for accommodating the collimating element 12, the shape and size of the first accommodating cavity are matched with those of the collimating element 12, and when the collimating element 12 is placed in the first accommodating cavity and the first housing 101 is connected with the second housing 102, the collimating element 12 is relatively fixed in the first accommodating cavity and does not move relatively. The first housing 101 and the second housing 102 may be connected by screws through holes. In addition, the first housing 101 and the second housing 102 may be connected by a screw connection or other means, as long as they can limit the collimating element 12 from moving relatively after being connected, and the utility model is not limited thereto.

A fixing sleeve 1031 is fixed in the third housing 103, the fixing sleeve 1031 is coaxially arranged with the third housing 103, and the fixing sleeve 1031 and the third housing 103 can be fixed by a connecting rod or the like, which is not limited in the present invention. The fixing sleeve 1031 is provided with a second accommodating cavity for accommodating the focusing element 13 therein, and the inner wall of the fixing sleeve 1031 can be stepped, so that the focusing element 13 is conveniently placed in the second accommodating cavity without sliding off. One end of the fixed sleeve 1031 is further provided with a limiting member 1032 for limiting the movement of the focusing element 13, and the limiting member 1032 is detachably connected with the fixed sleeve 1031. For example, the stopper 1032 is screwed to the fixing sleeve 1031, and after the stopper 1032 is fixed to the fixing sleeve 1031, the focusing element 13 is restricted by the inner wall of the fixing sleeve 1031 and the stopper 1032 so as not to move relatively. In this way, the optical axes of the focusing element 13 and the collimating element 12 are coaxial, which is helpful for focusing the laser introduced into the bone tissue ablation device 1 to the first focal point M, thereby ensuring the effect of cutting bone tissue by the laser. The third housing 103 and the second housing 102 can be connected with each other through an external thread on the outer side of the fixing sleeve 1031 and an internal thread of the second housing 102, and the connection manner between the third housing 103 and the second housing 102 is not limited here.

Since the first housing 101, the second housing 102, and the third housing 103 are detachably mounted, this can facilitate assembly of the bone tissue ablation device 1. In addition, the position of the first focal point M can be adjusted according to the difference of the optical parameters of the focusing element 13 and the collimating element 12, so that the adaptability of the present invention can be expanded, and different types of focusing elements 13 and collimating elements 12 can be selected according to different requirements.

In some examples, as shown in fig. 1, the second housing 102 is further provided with an air outlet 16, and the second housing has a first suction chamber, and the third housing 103 has a second suction chamber, and the second suction chamber is communicated with the suction port 15; wherein the first suction chamber and the second suction chamber jointly constitute the suction chamber. A sealing member is provided at the joint between the second housing 102 and the third housing 103. The seal is for example a sealing gasket.

The sealing element can ensure that the suction chamber has good air tightness, so that the air suction port 15 can have good air suction effect when the bone tissue ablation device 1 is used, and further the bone tissue cutting operation is facilitated.

In some embodiments, the laser inlet 11 is a carbon dioxide laser inlet or an erbium laser inlet. Namely, a carbon dioxide laser or an erbium laser is used for cutting the bone tissue.

Because the bone tissue carries water vapor, and the water can form cavitation bubbles due to photoinduced breakdown and thermoelastic effect after absorbing violent laser energy, and then the cavitation bubbles undergo a series of pulsating changes such as expansion, contraction and rebound, and finally collapse. In the whole process from cavitation pulsation to collapse, shock waves and broken jet flow can be generated, so that a mechanical effect is brought to bone tissues, and the bone tissues are polished and cut. Because the pathological change position of the bone tissue has more hydroxyapatite, and the energy in the activation medium of the carbon dioxide laser or the erbium laser slowly decays in the generation process, so that the carbon dioxide laser or the erbium laser can form a plurality of independent wavelengths, such as 9.3um, 9.6um, 10.3um and 10.6um lasers, and the lasers with the wavelengths are all positioned near the absorption peak of the hydroxyapatite and the secondary absorption peak of water, therefore, the bone tissue can achieve a good grinding and cutting effect.

The bone tissue ablation device can be particularly applied to correction surgery of the exophthalmos during the specific use process. The prominent eyeball is a deformity affecting the appearance, and the common causes are hyperthyroidism and myopia. In the related art, correction of the eyeball protrusion is mainly achieved by means of orbital decompression. Different operation types can be adopted for different patients, such as orbital posterior lateral wall grinding, wherein the orbital posterior lateral wall is ground by an electric drill to thin the orbital posterior lateral wall and the posterior inferior wall. These instruments, while helping the surgeon to resect the orbital walls and increase orbital volume, have some drawbacks in application as mentioned in the background. The bone tissue ablation device is utilized, so that the surgical field can be increased, the mechanical damage to the periphery of the eye socket in the surgical process is effectively avoided, the physical consumption of an operator caused by mechanical vibration is reduced, the probability of accidental injury to adjacent soft tissues is reduced, the wound caused by cutting the bone tissue is reduced, and the postoperative bone tissue repair is facilitated. Meanwhile, the bone tissue ablation device provided by the utility model can well remove the scraps generated in the cutting process, so that the parts needing to be subsequently resected can be more clearly exposed, and the process of the subsequent operation is facilitated; but also can take away the heat generated by cutting the bone tissue in time, thereby being beneficial to avoiding the heat damage of the part of heat to the bone tissue.

In addition, in the correction operation of the eyeball protrusion, since the operation visual field is limited and the action surface to the bone tissue is small, and the diameter of the circular covering surface (circular area) is between 3mm and 4mm, the absorption surface of the debris can be made reasonable, thereby facilitating the correction operation of the eyeball protrusion.

In addition, some embodiments of the present invention further provide a bone tissue ablation apparatus, which includes the bone tissue ablation device 1 according to some embodiments, and further includes a laser and negative pressure supply device 2, where the laser and negative pressure supply device 2 is provided with a laser interface and a trachea interface, the laser interface is connected with a laser inlet 11 of the bone tissue ablation device through an optical fiber 3, and the trachea interface is connected with an air outlet of the bone tissue ablation device through a trachea 4. Wherein the laser and negative pressure supply device 2 is configured to: providing a laser signal for a laser interface; and provides negative pressure to the tracheal interface. Of course, the laser and vacuum supply device 2 may be a combination of a single laser emitter and a single vacuum extractor.

Since the bone tissue ablation apparatus includes the bone tissue ablation device 1, it has all the effects that the bone tissue ablation device 1 can achieve, and the detailed description is omitted here.

In some embodiments, the laser and negative pressure supply device 2 may provide negative pressure to the trachea by means of air negative pressure, water negative pressure, or electric negative pressure. In the case where the vacuum extractor is provided independently of the laser emitter, the vacuum extractor may be an electric vacuum extractor.

In some examples, the optical fiber 3 may be an armored optical fiber, and the core inside the armored optical fiber may be well protected, and has strong pressure resistance and stretch resistance. And the air pipe 4 can adopt a PU high-pressure machine air pipe which resists negative pressure, thereby being beneficial to the introduction of negative pressure gas.

In addition, the bone tissue ablation device 1 can be controlled by a mechanical arm and a computer, so that microscopic and remote operations can be realized; meanwhile, the positioning and control precision of the operation can be further improved, and the cutting of any geometric shape can be carried out, so that the operation efficiency and effect can be further improved.

The above description is only for the specific embodiment of the present invention, but the scope of the present invention is not limited thereto, and any person skilled in the art can appreciate that changes or substitutions within the technical scope of the present invention are included in the scope of the present invention. Therefore, the protection scope of the present invention shall be subject to the protection scope of the appended claims.

Claims (10)

1. A bone tissue ablation device, comprising: a housing having a laser chamber and a suction chamber; the laser cavity is internally provided with a laser inlet and a laser outlet, a collimating element and a focusing element are sequentially arranged between the laser inlet and the laser outlet, and the collimating element is configured as follows: modulating laser light injected from the laser inlet into parallel laser light; the focusing element is configured to: focusing the parallel laser light emitted from the collimating element to a first focal point; the housing is further provided with a suction opening, and the suction opening is configured to: sucking the air outside the housing into the suction chamber along the suction direction of the suction port; the optical axis of the focusing element is perpendicular to a first plane where the first focus is located, and the part of the air suction port extending to the first plane along the air suction direction covers the first focus.

2. The bone tissue ablation device of claim 1, wherein a portion of the suction port extending in a suction direction to the first plane is a suction coverage surface, and the first focus is located within the suction coverage surface.

3. The bone tissue ablation device according to claim 2, wherein the air suction covering surface is a circular covering surface, the center of the circular covering surface coincides with the first focus, and the diameter of the circular covering surface is 3-4 mm.

4. The bone tissue ablation device of claim 1, wherein a portion of the suction port extending in a suction direction to the first plane is a second focal point, the second focal point coinciding with the first focal point.

5. The bone tissue ablation device according to any one of claims 1-4, wherein the suction chamber surrounds the laser chamber; and/or the air suction port is arranged around the laser outlet.

6. The bone tissue ablation device according to any one of claims 1 to 4, wherein the housing comprises a first housing, a second housing and a third housing which are detachably connected in sequence; the laser inlet is arranged at one end, far away from the second shell, of the first shell; the first housing and the second housing are connected to form a first accommodating cavity which can accommodate the collimating element, and the shape and the size of the first accommodating cavity are matched with those of the collimating element; be equipped with fixed cover in the third casing, be equipped with in the fixed cover and be used for holding focusing element's second holds the chamber, fixed cover one end still is equipped with and is used for the restriction the locating part of focusing element activity, the locating part with fixed cover can dismantle the connection.

7. The bone tissue ablation device of claim 6, wherein the second housing has an air outlet and the second housing has a first suction chamber, and the third housing has a second suction chamber, the second suction chamber being in communication with the suction port; and a sealing element is arranged at the joint between the second shell and the third shell.

8. The bone tissue ablation device according to any one of claims 1 to 4, wherein the laser inlet is a carbon dioxide laser inlet or an erbium laser inlet.

9. Bone tissue ablation equipment, comprising the bone tissue ablation device according to claims 1 to 8, further comprising a laser and negative pressure supply device, wherein the laser and negative pressure supply device is provided with a laser interface and an air pipe interface, the laser interface is connected with a laser inlet of the bone tissue ablation device through an optical fiber, and the air pipe interface is connected with an air outlet of the bone tissue ablation device through an air pipe.

10. The bone tissue ablation device of claim 9, wherein the optical fiber is an armored optical fiber; the air pipe is a high-pressure machine air pipe.

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