JP2014128313A - Surgical bone perforation drill stopper - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a surgical bone perforation drill stopper, which does not require outer diameter measurement for tubular bone in advance, ad can control a drill perforation distance by single hand operation in the process of drill operation, and avoid the risk that a drill blade punches through to the deepest part of the back of the bone overenthusiastically.SOLUTION: A drill stopper 1 is put onto a surgical drill 1 for perforating a tubular bone, which has collet chuck mechanisms 52, 56 for detachably holding a drill shaft 100 to transmit rotary drive, and a non-rotation end cap 55 for storing the collet chuck mechanisms. The drill stopper includes: a drill stopper body 2 which covers the end cap 55 of the surgical drill 50, and has an insertion hole 5 for inserting the drill shaft 100 held on the surgical drill 1; a non-rotation cylindrical part 3 which is fixed so as to communicate with the insertion hole 5 of the drill stopper body 2 and into which the drill shaft 100 can be inserted; and a drill connecting part 4 for connecting the drill stopper body 2 to the end cap 55.

Description

  The present invention is used by inserting a general-purpose shaft-shaped drill blade for drilling a tubular bone in an orthopedic surgical operation or the like in which a procedure for fixing a tubular bone due to a cause of a limb fracture or the like is required. The present invention relates to a drill-driven handpiece with a drill stopper used for the purpose of drilling bone while controlling the drilling depth of the drill with one-handed drill driving operation.

  In general, the tubular bone constitutes the limb skeleton such as the upper arm, forearm, thigh, and lower leg, and is composed of a soft bone marrow cavity in the center of the tube and a hard, tubular cortical bone that surrounds the bone. being called. In the operation of the tubular bone, a surgical technique or a surgical instrument different from the vertebra and the skull is used depending on the bone structure. For example, a tubular bone broken due to a fracture is reduced and fixed with several screws. For this purpose, it is necessary to drill a plurality of tubular bone through holes for screw insertion fixation. In other words, drilling is started from the surgically opened surgical field to the hard proximal bone cortex, which is the directly visible part of the tubular bone, and then drilled through the central soft bone marrow cavity to the hard contralateral bone cortex It is best to screw the two-stage hard cortical bone hole. And the drill drive for drill drilling does not affect only by hand rotation operation, drilling while controlling the direction and depth while holding the airway type or electric drill rotation drive body with the operator's hand Is required.

  When an operator manipulates such a power drill, when the drill penetrates the tubular bone, an important nerve that exists on the back side of the bone due to excessive penetration of the drill with a drill blade that penetrates too deeply into the back side of the bone. There is a risk of damaging blood vessels, muscle tendons.

  In order to avoid this risk, it has been attempted to calculate the diameter of the tubular bone or the like in advance by an X-ray photograph or the like, and to adjust the drill drilling distance to the calculated value before starting the drill. However, for tubular bones with a diameter of about 10 to 50 mm in general, the screw fixing direction must be changed depending on the direction of the fracture line, etc. Therefore, the drilling angle of the drill with respect to the tubular bone axis is not limited to a right angle but also in an oblique direction. It often happens. For this reason, the perforation distance can be as large as 10 mm or more when using only the diameter of a tubular bone that can be read in advance from a two-dimensional X-ray photograph or the like. It is hard to do.

  In order to minimize the risk by reducing the above error range to a few millimeters or less, when the tube bone contacts the contralateral bone cortex, which is the final hard wall that drills through, the general In particular, it is preferable to control the drilling distance by using the thickness of the contralateral bone cortex, which can be easily predicted as a difference of several millimeters depending on the surgical site and less than 10 mm. That is, it becomes necessary to control the drilling distance from the point of contact with the contralateral bone cortex during the operation of the bone drilling drill.

  Here, the surgeon operates the drill drive main body with one hand, but the other hand is often used for gripping muscles and fracture reduction forceps. It is preferable that the hand related to the drill drilling distance control in the middle stage is performed with the same hand as the drill driving main body operation.

  Conventionally, instruments that can adjust the axial length of a bone drilling drill or wire in the middle of the operation with the hand on the same side as operating the bone drilling power-driven handpiece are disclosed in Patent Documents 1 to 3 and the like. ing. These instruments are configured such that a drill shaft gripping or releasing by a so-called collet chuck can be operated by a lever or a trigger attached to a power-driven handpiece.

  Patent Document 4 includes a drill guide that senses the drilling of cortical bone in two stages of a tubular bone with an acceleration sensor or a torque sensor and controls it with two motors, a drill shaft rotation motor and a drill shaft direction drive motor. A one-handed operating device is disclosed.

JP-A-10-113884 JP 56-47616 A JP-A-62-236686 Special table 2011-525844 gazette

  However, the devices disclosed in the above documents have the following problems. Depending on the instrument disclosed in Patent Documents 1 to 3, the exposed length of the drill shaft protruding from the distal end is adjusted in line by several millimeters during the drilling operation in the surgical field from the structure of the distal end. It is difficult. Further, the distal end portion of the handpiece does not have a structure or a size to be brought into contact with the bone surface, is not described as a drill stopper, and cannot function as a stopper.

  In the device disclosed in Patent Document 4, an elongated guide is attached to the tip of a nozzle, a drill blade is mounted from the guide, and the guide receives the drill bit to guide the drill bit to be directed. However, the guide is used for drill orientation and is configured to move in the drill axis direction. That is, the elongated guide at the tip of the nozzle has a role of directing drill drilling, and does not function as a drill stopper. In addition, it is a mechanism that requires two motors, sensors, a display, a feedback function, etc., and is not a safe operation method by adjusting the insertion distance of the drill shaft by manually opening and closing the chuck.

  Therefore, the technical problem to be solved by the present invention is that a drilling operation using a pneumatic or electric drill drive main body for a tubular bone does not require an outer diameter measurement of the tubular bone in advance, and the drill Surgical bone drilling drill stopper for tubular bone drilling that can control the drilling distance with one hand operation by manual opening and closing method of collet chuck in the middle of operation and avoid the danger that the drill blade will pierce deeply into the back side of the bone And providing a surgical bone drill.

  In order to solve the above technical problem, the present invention provides a surgical bone drill drill stopper having the following configuration.

According to the first aspect of the present invention, a surgical drill for drilling a tubular bone having a collet chuck mechanism that grips and removes a drill shaft and transmits rotational driving and a non-rotatable end cap that houses the collet chuck function is covered. A drill stopper provided by fitting,
A drill stopper body covering an end cap of the surgical drill and having an insertion hole for inserting a drill shaft held by the surgical drill;
A non-rotatable tubular portion that is fixed in communication with the insertion hole of the drill stopper main body and is capable of inserting the drill shaft;
A surgical bone drill drill stopper, comprising: a drill coupling portion for coupling the drill stopper body to an end cap.

  According to a second aspect of the present invention, there is provided the surgical bone drilling drill stopper according to the first aspect, characterized in that the tubular portion is configured such that the distal end side becomes a partial peripheral wall.

  According to the third aspect of the present invention, the cylindrical portion determines the protruding length of the drill shaft from the tip of the cylindrical portion by indicating a predetermined position of the drill shaft in a longitudinal section of the partial peripheral wall. A surgical bone perforation drill stopper according to a second aspect is provided, characterized in that a scale is provided.

According to a fourth aspect of the present invention, there is provided a surgical bone drill for use in a surgical operation for drilling a through hole in a near bone cortex and a contralateral bone cortex of a tubular bone having a bone marrow cavity in the center,
A collet chuck mechanism that grips and removes the drill shaft and transmits rotation drive;
A non-rotating end cap that houses the collet chuck mechanism;
A non-rotatable cylindrical portion that is provided at a tip of the end cap and is capable of inserting the drill shaft;
A surgical bone drill is provided.

  According to a fifth aspect of the present invention, there is provided the surgical bone drill according to the fourth aspect, wherein the cylindrical portion is configured such that the distal end side becomes a partial peripheral wall.

  A surgical drill having a collet chuck mechanism in which the drill shaft can be easily attached and detached can fix and release the drill shaft only by manually tightening or releasing the lever of the collet chuck mechanism of the surgical drill, for example. For this reason, it is easy to change the protruding amount of the drill shaft during the drilling operation. Therefore, according to the present invention, the drilling depth can be controlled flexibly according to the situation during the drilling operation. For example, the drilling of the tubular bone advances, and the drill blade is formed on the inner wall surface of the contralateral bone cortex. At the stage when the collet chuck mechanism is operated, the drill shaft length that protrudes from the non-rotating cylindrical portion of the tip is adjusted, and by proceeding drilling in that state, when penetrating the contralateral bone cortex, At the same time that the tip of the drill blade protrudes slightly from the outer surface of the contralateral bone cortex, the drill can be stopped by the non-rotatable tubular portion contacting the front bone cortex surface. In addition, since the drill shaft is formed in an elongated shape and protrudes from the tip of the other cylindrical portion, it is easy to adjust the line of sight of the drill shaft in millimeters of less than 10 mm in the surgical field. Therefore, the exposure length of less than 10 mm can be controlled with higher accuracy than a device for perforating at a time with the overall outer diameter of the tubular bone as measured as a standard, which is as large as 10 to 50 mm.

  In addition, by configuring the distal end side of the cylindrical portion to be a partial peripheral wall, the area for concealing the drill shaft at the corner of the distal end of the cylindrical portion is reduced, and the distal end of the cylindrical portion and the drill shaft during the drilling operation are reduced. The visibility of the boundary line with the protruding portion can be improved. In that case, the length and wall supportability of the cylindrical portion to be brought into contact with the near bone cortex are maintained by the partial peripheral wall left at the tip.

  Furthermore, by providing a scale on the distal end side of the cylindrical portion, the exposed length of the drill can be seen and grasped in the surgical field, and excessive penetration of the drill can be more effectively prevented.

1 is an exploded view showing a configuration of a surgical drill to which a surgical bone drill drill stopper according to a first embodiment of the present invention is applied. It is a perspective view which shows the structure of the surgical bone drill drill stopper concerning 1st Embodiment of this invention. It is a schematic diagram which shows the state which starts drilling the near side bone cortex with the drill blade which attached the drill stopper of FIG. It is a schematic diagram which shows the state which the drill blade which attached the drill stopper of FIG. 1 reached the contralateral bone cortex inner wall surface. It is a schematic diagram which shows position adjustment of the outer cylinder part of the drill stopper of FIG. It is a schematic diagram which shows the state which the drill blade which attached the drill stopper of FIG. 1 penetrated the contralateral bone cortex. It is a figure which shows the difference in the drill drilling | drilling path | route by the difference in a drill direction. It is a perspective view which shows the structure of the surgical bone drill drill stopper concerning 2nd Embodiment of this invention. It is an assembly exploded view which shows the structure of the surgical drill concerning the modification of this invention.

  Hereinafter, a surgical bone drill drill stopper according to each embodiment of the present invention will be described with reference to the drawings.

(First embodiment)
FIG. 1 is an exploded view showing a configuration of a surgical drill to which a surgical bone drill drill stopper according to a first embodiment of the present invention is applied. The surgical drill 50 is an instrument for piercing human tissue, preferably tubular bone, and has a main body 51 that houses a drive motor (not shown). The drive motor supplies a driving force to a rotary shaft (not shown), The collet shaft 52 connected to the rotation shaft is rotated. The drive motor is driven by supplying power, but for example, a pneumatic motor driven by high-pressure gas can be used.

  The main body 51 has a pistol-type grip 53, and the drive motor rotates by operating an operation switch 54 provided on the grip 53. The drive motor may be configured such that the rotational speed changes in proportion to the amount of pressing of the operation switch 54, or may be configured to rotate at a constant speed regardless of the amount of pressing of the operation switch.

  When the drive motor rotates, the collet shaft 52 rotates via a rotation shaft (not shown). The collet shaft 52 is divided by a slit extending in the axial direction, and the tip is tapered. The drill shaft 100 is inserted into the collet shaft 52, and the tapered portion is pressed against the end cap 55, whereby the slit portion of the collet shaft 52 is closed and the drill shaft 100 is gripped.

  The end cap 55 is provided with a hole through which the drill shaft 100 is inserted, and is fixed to the main body 51 with the collet shaft 52 in a housed state. Even when the drill shaft 100 is driven, the end cap 55 is separated from the rotational motion of the drill shaft or the collet shaft by a known bearing mechanism or the like, and is configured to be non-rotatable.

  The lever 56 is for switching between gripping and releasing the drill shaft 100 of the collet shaft 52. The lever 56 and the collet shaft 52 are connected so that the collet shaft 52 moves in the axial direction by operating the lever 56 to the grip 53 side, and the collet shaft 52 moves to the axial front end side. The tapered portion of the collet shaft 52 is tightened by the end cap 55, and the drill shaft 100 is gripped. Since the collet shaft 52 is configured to be driven to rotate by the drive motor as described above, the connection between the collet shaft 52 and the lever 56 is performed by rotating the collet shaft 52 or the drill shaft by a known bearing mechanism or the like. It is configured to ensure.

  According to the surgical drill 50 having the collet chuck mechanism configured as described above, the drill shaft 100 can be easily grasped and released by operating the lever 56. As shown in FIG. 1, the lever 56 is configured to be able to be gripped while gripping the grip 53. The lever 56 is operated with, for example, the middle finger and the ring finger of the hand holding the grip, and the collet shaft 52 is moved to the distal end side by being pulled toward the grip 53, so that the collet shaft 52 can be closed and the drill shaft 100 can be gripped. In this state, the drill shaft 100 can be rotated by operating the operation switch 54 with the index finger of the hand holding the grip 53. The lever 56 may be configured so that it can be fixed or released at any time while the drill shaft 100 is held by a known mechanism such as a ratchet mechanism.

  The length dimension and the diameter dimension of the drill shaft 100 can be appropriately selected depending on the treatment site and the like, and the surgical drill 50 corresponding to the size of the drill can be used. Further, the drill shaft 100 is configured to have a uniform diameter from the tip to the tail end, and can be freely inserted and moved through the main body 51 including a drive motor from the tip to the tail end. Yes.

  FIG. 2 is a perspective view showing the configuration of the surgical bone drill drill stopper according to the first embodiment of the present invention. As shown in FIG. 2, the surgical bone drilling drill stopper 1 according to the present embodiment includes a drill stopper main body 2, a cylindrical portion 3, and a drill connecting portion 4.

  The drill stopper main body 2 is a cap-shaped member that covers the end cap 55 of the surgical drill 50, and the drill shaft 100 held by the collet shaft 52 of the surgical drill 50 from the insertion hole 5 provided on the distal end side. Is inserted. In the description of the embodiments, the front end side means the pointed end side of the drill shaft, and the rear end side means the surgical drill side.

  A slit 6 for fixing the drill stopper main body 2 to the end cap 55 is provided on the rear side of the drill stopper main body 2, and a fixing piece 7 is formed on the rear side of the slit 6. The fixed piece 7 is configured integrally with the drill connecting portion 4, and the fixed piece 7 is fixed to the tightened end cap 55 by tightening the screw 8 of the drill connecting portion 4. In addition, the structure of the drill connection part 4 is not limited to what is shown to this embodiment, For example, it is also possible to fix using the clamping screw etc. which were provided in the drill stopper main body 2. FIG.

  The cylindrical portion 3 is a cylindrical member that is provided on the distal end side of the drill stopper main body 2 and is configured to be able to pass through the drill shaft 100 in communication with the insertion hole 5. The length L of the cylindrical portion 3 can be set to 2 to 5 cm, for example, and can be appropriately designed according to the size of the drill stopper main body 2 and the length of the drill shaft 100 to be used.

  The distal end side of the cylindrical part 3 is configured as a partial peripheral wall part 9 in which only a part of the peripheral wall is formed. The dimension of the partial peripheral wall part 9 is not specifically limited, For example, it can also comprise in a partial peripheral wall over the substantially full length of a cylindrical part. By providing the partial peripheral wall portion 9 at the distal end of the cylindrical portion 3, as will be described later, the visibility of the boundary line between the protruding portion of the drill shaft 100 and the distal end of the cylindrical portion in the operative field is improved, and the drill operation is facilitated. can do.

  In addition, in this embodiment, the partial surrounding wall part 9 is comprised so that the surrounding wall by the side in which the drill connection part 4 is provided may be left. By eliminating the peripheral wall on the side where the drill connecting portion 4 is not provided, it is possible to prevent the drill connecting portion 4 from making the drill shaft 100 difficult to visually recognize, and the operability is further improved. In addition, the drill stopper body 2 can be fixed at an arbitrary rotation angle with respect to the drill shaft by the drill stopper connecting portion 4, and the visibility by the direction of the partial peripheral wall is considered depending on whether the drilling operation is the right hand or the left hand or the surgical field direction. Can be connected and fixed.

  Next, a procedure for using the surgical bone drill drill stopper according to this embodiment will be described. As shown in FIG. 3, the surgical bone drill drill stopper according to the present embodiment inserts the drill shaft 100 into the cylindrical portion 3, and the drill shaft 100 has a sufficient protruding amount from the tip of the cylindrical portion 3. After adjusting the exposure length, the lever 56 of the surgical drill 50 is held and the drill shaft 100 is fixed. At the start of drilling, in order to ensure the visibility of the tip side of the drill shaft 100, it is preferable to increase the exposed length of the tip side of the drill shaft 100.

  Next, as shown in FIG. 4, drilling of the tubular bone 110 to be drilled is started. The tubular bone 110 is composed of a tubular cortical bone 111 and a central bone marrow cavity 112. Among the bone cortex 111, the bone cortex on the side to which the drill is applied from the outside in the surgical field where the skin was incised at the start of drilling is the bone cortex 113 on the near side, the bone marrow cavity 112 penetrating through the bone cortex, and the inside of the lumen For convenience, the bone cortex to which the drill is applied is distinguished from the contralateral bone cortex 114. Since the cylindrical part 3 is fixed without rotating at the time of drilling, there is no particular problem such as involving other surrounding tissues in the drilling operation.

  In drilling, the distal end of the drill shaft 100 is applied to the surface of the front bone cortex 113, and the hard front bone cortex 113 is drilled while operating the drill device to control the direction of drilling. In addition, in order to determine the drilling direction of a drill, other instruments, such as a drilling guide, can also be used. The perforation of the near-side bone cortex 113 is an intrusion into the bone marrow cavity 112 to be passed through, so it is safe to drill with vigor.

  In addition, in this drilling, a drilling guide or the like can be used separately. As described above, since the drill stopper according to the present embodiment can be operated with only one hand that holds the surgical drill, it is possible to use the other hand for holding the stamen or the fracture reduction forceps.

  FIG. 5 shows a state in which the tip 100a of the drill shaft 100 is in contact with the inner wall surface of the contralateral bone cortex 114 with a hard resistance after passing through the front bone cortex 113 and further passing through the bone marrow cavity 112. Yes. In drilling with a drill, when the drill blade tip 100a penetrates the near bone cortex 113 with a hard resistance and reaches the bone marrow cavity 112, the drill resistance is weakened, and when reaching the hard contralateral cortical bone 114 again, the drill resistance becomes strong. It is easily sensed by the operator's hand holding the drill drive body. At that time, the rotation of the drill is temporarily stopped, and the lever 56 is loosened with the tip 100a of the drill shaft 100 held in contact with the inner wall surface of the contralateral cortical bone 114 as shown in FIG. The drill 50 is fed to the tubular bone side as indicated by an arrow 90, and the distance H between the distal end of the tubular portion 3 and the surface of the near-side bone cortex 113 is approximately the thickness dimension of the contralateral bone cortex 114. adjust.

  Since the near-side bone cortex 113 has already been penetrated, the surgeon can easily predict the thickness dimension of the contralateral bone cortex based on the basic anatomical basis described later, and the distal end of the tubular portion 3 and the near-side It can be used as a guide when setting the distance H to the surface of the side bone cortex 113.

  After adjusting the amount of projection of the drill shaft from the tubular portion 3, the contralateral bone cortex 114 is drilled. At this time, since the partial peripheral wall portion 9 is provided at the distal end of the cylindrical portion 3, the drill can be clearly seen without being concealed by the drill protrusion boundary line at the distal end corner portion of the cylindrical portion 3 in the surgical field. The amount of protrusion can be adjusted in mm units, and the treatment can be performed accurately and smoothly. As shown in FIG. 6, after penetrating the contralateral bone cortex 114, the tip of the cylindrical portion 3 abuts on the surface of the near-side bone cortex 113, so that the drill does not advance beyond the adjusted gap H, and is excessive. Drilling is suppressed. Therefore, the progress of the drill tip 100a immediately after penetrating the contralateral bone cortex 114 of the tubular bone can be stopped, and damage to important nerves, blood vessels, muscle tendon tissues and the like located on the back side of the tubular bone can be prevented. can do.

  According to the surgical bone drill drill stopper 1 according to the present embodiment, it is possible to eliminate the need for measuring the outer diameter of the tubular bone in advance based on the basic anatomical basis described below. That is, the outer diameter of the human limb tubular bone varies depending on the physique and may be 50 mm or more, but the thickness of the tubular bone cortex that forms the tubular structure is approximately several mm even in the upper arm, forearm, thigh, and lower leg. In the following, the variation difference in the range is easily estimated by the preoperative physique and limb part of the patient, and even if the drill direction is tilted by about 45 degrees, the error is several mm or less. This variation difference is clearly less than when drilling with the entire outer diameter of the tubular bone as a guide. In other words, in the drilling of a tubular bone drill, it is not necessary to measure the outer diameter of the tubular bone in advance, drilling from the near bone cortex to the central bone marrow cavity, and the tip of the drill blade with a hard resistance to the inner wall of the contralateral bone cortex If the thickness of the remaining tubular bone cortex is predicted based on the above anatomical basis and the drill drilling distance is controlled, the excessive drill penetration can be suppressed with an error of several millimeters or less as described above. Is possible.

  Specifically, as shown in FIG. 7, (1) the drilling path when the drill direction passes through the central axis of the tubular bone and (2) when the drill direction deviates from the central axis, and (3) the axial direction of the tubular bone (4) For drill drilling paths when tilted, the error is reduced by using the thickness d of the contralateral bone cortex as a guide rather than using the outer diameter D of the tubular bone as a guide. Obviously it can be.

  Furthermore, according to the surgical bone drilling drill stopper 1 according to the present embodiment, the drill shaft can be easily grasped and released by operating the lever 56, and it is not necessary to hold the stopper, so that it can be performed with one hand. It is. Therefore, other instruments such as forceps can be operated with a free hand to improve the degree of freedom of the operation.

(Second embodiment)
FIG. 8 is a perspective view showing the configuration of the surgical bone drill drill stopper according to the second embodiment of the present invention. FIG. 8 shows a state in which the drill shaft 100 is inserted for understanding. Since the surgical bone drilling drill stopper 11 according to the present embodiment has the same configuration as the surgical bone drilling drill stopper 1 according to the first embodiment, the following description will be focused on the differences.

  As shown in FIG. 8, the surgical bone drill drill stopper 11 according to the present embodiment is different from the surgical bone drill drill stopper 1 according to the first embodiment in the configuration of the tubular portion 13. That is, as shown in FIG. 8, the surgical bone drilling drill stopper 11 according to the present embodiment has a long partial peripheral wall portion 19, and a scale 20 in millimeters is provided on the longitudinal section of the partial peripheral wall portion 19. It has been.

  The scale 20 is for determining the amount of projection of the drill shaft 100 from the tip of the tubular portion 13 by making it correspond to a reference mark 105 provided at a predetermined position of the drill shaft 100. That is, the reference mark 105 is provided at a predetermined position from the tip of the drill shaft 100, and the scale 20 is configured such that the numerical value of the scale 20 that matches the reference mark 105 becomes the protruding amount of the drill shaft 100. .

  According to the present embodiment, when the drilling is finished with a safe and appropriate penetration distance and the bone fixing metal screw is inserted into the drilled part and the surgical operation is advanced as the next operation stage, the length of the metal screw is the previous paragraph. Therefore, it is possible to omit the conventional drilling distance measurement using a depth gauge or the like. Further, when it is desired to make the protruding amount of the drill shaft 100 a predetermined length, the adjustment of the drilling depth of the drill can be facilitated by using the scale 20.

  In addition, this invention is not limited to the said embodiment, It can implement in another various aspect. For example, in each embodiment, the drill stopper is attached by being fitted to the end cap of the surgical drill. However, as shown in FIG. 9, the end cap 55 itself of the surgical drill is not rotated. A portion 57 can be provided.

DESCRIPTION OF SYMBOLS 1,11 Surgical bone drilling drill stopper 2,12 Drill stopper main body 3,13,56 Cylindrical part 4,14 Drill connection part 5,15 Insertion hole 6,16 Slit 7,17 Fixing piece 8,18 Screw 9,19 Partial peripheral wall 50 Surgical drill 51 Main body 52 Collet shaft 53 Grip 54 Operation switch 55 End cap 56 Lever 90 Direction of pushing the surgical drill 100 Drill blade 100a Drill blade tip 100b Drill blade intermediate portion 105 Reference mark 110 Tubular bone 111 Bone Cortex 112 Bone Marrow Cavity 113 Front Bone Cortex 114 Contralateral Bone Cortex

Claims (5)

A drill stopper provided to be fitted on a surgical drill for drilling a tubular bone having a collet chuck mechanism for gripping and detaching a drill shaft and transmitting rotational driving, and a non-rotatable end cap for housing the collet chuck mechanism. ,
A drill stopper body covering an end cap of the surgical drill and having an insertion hole for inserting a drill shaft held by the surgical drill;
A non-rotatable tubular portion that is fixed in communication with the insertion hole of the drill stopper main body and is capable of inserting the drill shaft;
A surgical bone drill drill stopper, comprising: a drill coupling portion for coupling the drill stopper body to an end cap.   The surgical bone perforation drill stopper according to claim 1, wherein the cylindrical portion is configured such that a distal end side thereof becomes a partial peripheral wall.   The cylindrical portion is provided with a scale for determining a protruding length of the drill shaft from the tip of the cylindrical portion by indicating a predetermined position of the drill shaft on a longitudinal section of the partial peripheral wall. The surgical bone drill drill stopper according to claim 2, characterized in that it is characterized in that: A surgical bone drill for use in a procedure for drilling a through-hole in the proximal bone cortex and the contralateral bone cortex of a tubular bone having a bone marrow cavity in the center,
A collet chuck mechanism that grips and removes the drill shaft and transmits rotation drive;
A non-rotating end cap that houses the collet chuck function;
A non-rotatable cylindrical portion that is provided at a tip of the end cap and is capable of inserting the drill shaft;
Surgical bone drilling drill characterized by comprising. The surgical bone perforation drill according to claim 4, wherein the cylindrical portion is configured such that a distal end side thereof becomes a partial peripheral wall.

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