WO1996041573A1 - Self-drilling bone securing component - Google Patents

Self-drilling bone securing component Download PDF

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Publication number
WO1996041573A1
WO1996041573A1 PCT/CH1996/000210 CH9600210W WO9641573A1 WO 1996041573 A1 WO1996041573 A1 WO 1996041573A1 CH 9600210 W CH9600210 W CH 9600210W WO 9641573 A1 WO9641573 A1 WO 9641573A1
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WO
WIPO (PCT)
Prior art keywords
fixation element
bone fixation
element according
bone
thread
Prior art date
Application number
PCT/CH1996/000210
Other languages
German (de)
French (fr)
Inventor
Robert Frigg
Markus Hehli
Original Assignee
Synthes Ag Chur
Synthes (U.S.A.)
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Synthes Ag Chur, Synthes (U.S.A.) filed Critical Synthes Ag Chur
Publication of WO1996041573A1 publication Critical patent/WO1996041573A1/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/84—Fasteners therefor or fasteners being internal fixation devices
    • A61B17/86—Pins or screws or threaded wires; nuts therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
    • A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/70—Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/80—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates
    • A61B17/8061—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates specially adapted for particular bones
    • A61B17/8071—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates specially adapted for particular bones for the jaw
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
    • A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
    • A61B2017/0414—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors having a suture-receiving opening, e.g. lateral opening
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
    • A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
    • A61B2017/044—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors with a threaded shaft, e.g. screws
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/08—Muscles; Tendons; Ligaments
    • A61F2/0811—Fixation devices for tendons or ligaments
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/28—Bones
    • A61F2/2803—Bones for mandibular reconstruction

Definitions

  • the invention relates to a bone fixation element according to the preamble of patent claim 1.
  • Bone fixation elements in particular in the form of bone screws, are widely used in osteosynthesis.
  • bone fixation element that can be inserted quickly and safely into the bone and serves as an anchor.
  • the first area concerns the jaw area, in which mini screws are required for tooth position corrections.
  • the second area concerns the need for a bone anchor for the fixation of ligaments and tendons.
  • the conventional insertion method in which the thread of the bone screws to be used has to be pre-drilled in the bone in a first step, has proven to be two-time-consuming and complicated, in particular with the small screw dimensions used here.
  • the thread pitch of a bone screw is critical because it determines the cutting speed, ie the feed of the screw, in other words, the screw is forced forward by the height of the thread pitch per revolution. If a thread pitch of approx. 1.75 mm, which is common for bone screws, is used, the drill tip must drill through the bone over a distance of 1.75 mm per revolution. At a normal speed of rotation of a drilling machine used in bone surgery of approx.
  • wires can be screwed into the bone without major preparatory work, they damage the bone due to the high temperatures that occur as a result of the friction between the bone and the wire. Furthermore, the axial stability of bone fragments fixed with wires is not very high, so that the reduction can be lost.
  • the invention seeks to remedy this.
  • the invention has for its object to provide a fixation element which can be inserted into the bone without any preliminary work.
  • the invention solves the problem with a bone fixation element, which has the features of claim 1. Further advantageous embodiments of the invention are characterized in the dependent claims.
  • the front part of the bone fixation element designed as a drill, is expediently designed as a self-tapping, self-drilling, two-lip spiral drill, the outer diameter of which is at most as large as the thread core diameter.
  • the front part expediently has a length of 3 to 18 mm, preferably 4 to 12 mm.
  • Method 1 Volume 1, page 146 (Verlag Otto Walter AG, ⁇ lten, 1950).
  • FIG. 1 shows a schematic illustration of the bone fixation element according to the invention
  • FIG. 2 shows an axial plan view of the bone fixation element according to FIG. 1;
  • FIG. 3 shows a detailed longitudinal section through the thread of the bone fixation element according to FIG. 1;
  • Figure 4 is a section on the line A-A of Figure 1;
  • FIG. 5 shows a schematic illustration of a further embodiment of the bone fixation element according to the invention.
  • FIG. 6 shows an axial top view of the bone fixation element according to FIG. 5;
  • FIG. 7 shows a detailed longitudinal section through the thread of the bone fixation element according to FIG. 5;
  • FIGS. 1-4 show an axial view from below of the bone fixation element according to FIG. 5.
  • the bone fixation element shown in FIGS. 1-4 essentially consists of a head end 1, a shaft part 3 provided with a thread 2 and a front part 4 with a tip 5.
  • the bone fixation element also has a longitudinal axis 7.
  • the front part 4 is designed as a self-tapping, self-drilling, double-lip twist drill 11, whose outer diameter d is smaller than the core diameter D of the thread 2, which extends into the front part 4.
  • the front part 4 has a length of 7-9 mm.
  • the head end 1 is - as shown in Fig. 2 - provided with a central recess 6, in the form of a hexagon socket, which serves to hold an insertion tool.
  • the head end 1 furthermore has a channel running transversely to the longitudinal axis 7 in the form of a through hole 8, which intersects the longitudinal axis 7 perpendicularly.
  • the diameter of the through bore 8 should be approximately 35-50%, preferably 39-44% of the diameter of the head end 1 or of the shaft part 3.
  • the through hole 8 serves to receive a thread or a wire with which either several bone fixation elements can be connected to one another or further osteosynthetic elements or anatomical structures can be anchored to the bone.
  • the bone fixation element can be provided with an outer groove 10 which runs peripherally on the outside 9 of the head end 1 and which runs coaxially to the longitudinal axis 7.
  • the outer groove 10 serves the same purpose as the through hole 8, ie for receiving a thread or wire.
  • the through bore 8 is designed as a slot which is open at the top.
  • the through hole 8, as shown in FIG. 5, is arranged in the shaft part 3 instead of in the head end 1, which in this embodiment has no external groove.
  • the head end 1 has a cross slot 12, which is used to hold an insertion tool, in particular a screwdriver.
  • the bone fixation elements according to the invention can be carried out directly by the surgeon, i.e. without pre-drilling, using a suitable insertion tool, e.g. B. a hexagon, or Phillips screwdriver in the bone.
  • a suitable insertion tool e.g. B. a hexagon, or Phillips screwdriver in the bone.

Abstract

The bone securing component comprises a head end (1), a shank section (3) with a thread (2) and a front section (4) with a point (5) in the form of a drill. The head end (1) has a channel (8, 10) in the form of a through drilling (8) and/or an outer groove (10) running transversely to the longidutinal axis (7) and capable of accepting a thread or a wire.

Description

Selbstbohrendes KnochenfixationselementSelf-drilling bone fixation element
Die Erfindung bezieht sich auf ein Knochenfixationselement gemäss dem Oberbegriff des Patentanspruchs 1.The invention relates to a bone fixation element according to the preamble of patent claim 1.
Knochenfixationselemente, insbesondere in Form von Knochen¬ schrauben finden in der Osteosynthese in weiten Bereichen Anwendung. Trotz der vielfältigen Ausführungsformen bekannter Knochensehrauben besteht auf zwei speziellen Gebieten ein Bedarf nach einem schnell und sicher in den Knochen einbringbaren als Anker dienendes Knochenfixationselement.Bone fixation elements, in particular in the form of bone screws, are widely used in osteosynthesis. In spite of the diverse embodiments of known bone spikes, there is a need in two special fields for a bone fixation element that can be inserted quickly and safely into the bone and serves as an anchor.
Das erste Gebiet betrifft den Kieferbereich, in welchem Minischrauben für Zahnstellungskorrekturen gefragt sind. Das zweite Gebiet betrifft den Bedarf nach einem Knochenanker zur eichteilrefixation von Bändern und Sehnen.The first area concerns the jaw area, in which mini screws are required for tooth position corrections. The second area concerns the need for a bone anchor for the fixation of ligaments and tendons.
Für beide Applikationen hat sich die herkömmliche Einbring¬ methode, bei welcher dass Gewinde der zu verwendenden Knochenschrauben in einem ersten Schritt im Knochen vorgebohrt werden muss, als zweitaufwendig und kompliziert erwiesen, im besonderen bei den hier verwendeten kleinen Schrauben- dimensionen. ie Gewindesteigung einer Knochenschraube ist kritisch, da sie die Schnittgeschwindigkeit, d.h. den Vorschub der Schraube bestimmt, mit anderen Worten, die Schraube wird pro Umdrehung um die Höhe der Gewindesteigung nach vorne gezwungen. Wird eine, für Knochenschrauben übliche Gewindesteigung von ca. 1,75 mm verwendet, so muss die Bohrerspitze pro Umdrehung auf einer Strecke von 1,75 mm den Knochen durchbohren. Bei einer üblichen Umdrehungszahl einer in der Knochenchirurgie verwendeten Bohrmaschine von ca. 600 - 800 U/min entspricht dies einem Vorschub der Schraube von über einem Meter pro Minute. Der durch diesen Vorschub bedingte, ausserordentlich grosse Druck der Bohrerspitze auf den Knochen, kann Spontanrisse oder Frakturen im Knochen bewirken. Der Hauptnachteil eines zu grossen Schraubenvorschubes zeigt sich vor allem dann, wenn die Bohrerspitze die nahe Kortikalis und den Markraum durchdrungen hat und auf die Innenseite der Gegenkor ikalis trifft. Dort hat die Bohrerspitze keine Gelegenheit, sich zu zentrieren und den sogenannten Anschnitt zu tätigen. Statt den Knochen zu durchbohren, wird dieser durch die Schraubenspitze weggestossen. Dies führt unweigerlich zu einem Bersten der Gegenkortikalis. Wenn die Schraube nahe der Fraktur eingebracht wird, entlädt sich der aufgebrachte Druck durch Längsspaltung der Gegenkortikalis.For both applications, the conventional insertion method, in which the thread of the bone screws to be used has to be pre-drilled in the bone in a first step, has proven to be two-time-consuming and complicated, in particular with the small screw dimensions used here. The thread pitch of a bone screw is critical because it determines the cutting speed, ie the feed of the screw, in other words, the screw is forced forward by the height of the thread pitch per revolution. If a thread pitch of approx. 1.75 mm, which is common for bone screws, is used, the drill tip must drill through the bone over a distance of 1.75 mm per revolution. At a normal speed of rotation of a drilling machine used in bone surgery of approx. 600 - 800 rpm, this corresponds to an advancement of the screw of more than one meter per minute. The extremely high pressure of the drill tip on the bone caused by this advance can cause spontaneous cracks or fractures in the bone. The main disadvantage of an excessively large screw feed is particularly evident when the drill tip has penetrated the nearby cortex and medullary canal and meets the inside of the counter cortex. There the drill tip has no opportunity to center itself and make the so-called first cut. Instead of piercing the bone, it is pushed away by the screw tip. This inevitably causes the counter cortex to rupture. If the screw is inserted near the fracture, the pressure applied is released by longitudinal splitting of the opposite cortex.
Der Versuch den axialen Druck durch Reduktion der Bohrmaschinendrehzahl zu verkleinern ist nicht möglich, da der Vorschub durch die Gewindesteigung der Schraube vorgegeben ist. Die Arbeitsvorgänge zum Einbringen der Knochenschrauben sind aber auch umfangreich. Das Schraubenloch muss zuerst mit einem ersten Instrument aufgebohrt werden, dann muss mit einem zweiten Instrument das Gewinde geschnitten werden und schliesslich kann in einem dritten Arbeitvorgang die Knochenschraube eingedreht werden. Auch werden übliche Knochenschrauben nicht selten bis an die Grenze ihrer Haltekraft angezogen. Durch die oft sehr hohe Vorspannung bis an die Grenze der Haltekraft kann es vorkommen, dass die Schrauben aus dem Knochen ausreissen.Attempting to reduce the axial pressure by reducing the drilling machine speed is not possible because the feed is determined by the thread pitch of the screw. The work processes for inserting the bone screws are also extensive. The screw hole must first be drilled out with a first instrument, then the thread must be cut with a second instrument and finally the bone screw can be screwed in in a third operation. Common bone screws are also often tightened to the limit of their holding force. Due to the often very high prestress to the limit of the holding force, the screws can tear out of the bone.
Während der oben beschriebenen ArbeitVorgänge können sich zudem Fehler häufen und es kommt zu einer schlechten Fixation.Errors can also accumulate during the above-described work processes and poor fixation occurs.
Drähte können zwar ohne grossere Vorarbeiten in den Knochen eingedreht werden, schädigen den Knochen aber durch die dabei auftretenden hohen Temperaturen, welche durch die Reibung zwischen Knochen und Draht entstehen. Des weiteren ist die axiale Stabilität von mit Drähten fixierten Knochenfragmenten nicht sehr hoch, so das es zum Verlust der Reposition kommen kann.Although wires can be screwed into the bone without major preparatory work, they damage the bone due to the high temperatures that occur as a result of the friction between the bone and the wire. Furthermore, the axial stability of bone fragments fixed with wires is not very high, so that the reduction can be lost.
Hier will die Erfindung Abhilfe schaffen. Der Erfindung liegt die Aufgabe zugrunde, ein Fixationselement zu schaffen, welches ohne Vorarbeiten in den Knochen eingebracht werden kann. Die Erfindung löst die gestellte Aufgabe mit einem Knochenfixationselement, welches die Merkmale des Anspruchs 1 aufweist. Weitere vorteilhafte Ausgestaltungen der Erfindung sind in den abhängigen Ansprüchen gekennzeichnet.The invention seeks to remedy this. The invention has for its object to provide a fixation element which can be inserted into the bone without any preliminary work. The invention solves the problem with a bone fixation element, which has the features of claim 1. Further advantageous embodiments of the invention are characterized in the dependent claims.
Das als Bohrer ausgebildete Vorderteil des Knochenfixations- elementes ist zweckmassigerweise als selbstschneidender, selbstbohrender, zweilippiger Spiralbohrer ausgebildet, dessen Aussendurchmesser höchstens so gross ist als der Gewindekerndurchmesser. Das Vorderteil weist zweckmassigerweise eine Länge von 3 bis 18 mm, vorzugsweise von 4 bis 12 mm, auf.The front part of the bone fixation element, designed as a drill, is expediently designed as a self-tapping, self-drilling, two-lip spiral drill, the outer diameter of which is at most as large as the thread core diameter. The front part expediently has a length of 3 to 18 mm, preferably 4 to 12 mm.
Für den als Bohrer ausgebildeten Vorderteil sollte vorteil¬ hafterweise die nachstehende Geometrie eingehalten werden.For the front part designed as a drill, the following geometry should advantageously be adhered to.
Spitzenwinkel 60° bis 120°, vorzugsweise 80 - 90o .Point angle 60 ° to 120 °, preferably 80 - 90o.
Steigungswinkel 10° - 40°, vorzugsweise 20 - 30°; Fasenbreite 0,2 mm - 1,0 mm, vorzugsweise 0,3 mm - 0,6 mm,- Gewindehöhe 0,2 mm - 1,5 mm, vorzugsweise 0,6 mm - 0,8 mm; Bohrerseele das 0,1 - 0,6-fache, vorzugsweise das 0,3 bis 0,5-fache des Bohrerdurchmessers in Abhängig¬ keit des Werkstoffs. Bezüglich der Bohrer-Terminologie wird auf das Werk "Metallbearbeitung", Band 1, Seite 146 (Verlag Otto Walter AG, Ölten, 1950) verwiesen.Pitch angle 10 ° - 40 °, preferably 20 - 30 °; Chamfer width 0.2 mm - 1.0 mm, preferably 0.3 mm - 0.6 mm, thread height 0.2 mm - 1.5 mm, preferably 0.6 mm - 0.8 mm; Drill core 0.1 - 0.6 times, preferably 0.3 to 0.5 times the drill diameter depending on the material. With regard to drill terminology, reference is made to the work "Metalworking", Volume 1, page 146 (Verlag Otto Walter AG, Ölten, 1950).
Die Erfindung und Weiterbildungen der Erfindung werden im folgenden anhand der teilweise schematischen Darstellungen eines Ausführungsbeispiels noch näher erläutert. igen :The invention and further developments of the invention are explained in more detail below on the basis of the partially schematic representations of an exemplary embodiment. own:
Fig. 1 eine schematische Darstellung des erfindungs- gemässen Knochenfixationselementes;1 shows a schematic illustration of the bone fixation element according to the invention;
Fig. 2 eine axiale Aufsicht auf das Knochen¬ fixationselement nach Fig. 1;FIG. 2 shows an axial plan view of the bone fixation element according to FIG. 1;
Fig. 3 einen Detail-Längsschnitt durch das Gewinde des Knochenfixationselementes nach Fig. 1;3 shows a detailed longitudinal section through the thread of the bone fixation element according to FIG. 1;
Fig. 4 einen Schnitt längs der Linie A-A von Fig. 1;Figure 4 is a section on the line A-A of Figure 1;
Fig. 5 eine schematische Darstellung einer weiteren Ausführungsform des erfindungsgemässen Knochenfixations¬ elementes;5 shows a schematic illustration of a further embodiment of the bone fixation element according to the invention;
Fig. 6 eine axiale Aufsicht von oben auf das Knochen¬ fixationselement nach Fig. 5;6 shows an axial top view of the bone fixation element according to FIG. 5;
Fig. 7 einen Detail-Längsschnitt durch das Gewinde des Knochenfixationselementes nach Fig. 5; und7 shows a detailed longitudinal section through the thread of the bone fixation element according to FIG. 5; and
Fig. 8 ein axiale Ansicht von unten auf das Knochen¬ fixationselement nach Fig. 5. Das in den Fig. 1 - 4 dargestellte Knochenfixationselement besteht im wesentlichen aus einem Kopfende 1, einem mit einem Gewinde 2 versehenen Schaftteil 3 und einem Vorderteil 4 mit Spitze 5. Das Knochenfixationselement weist im übrigen eine Längsachse 7 auf.8 shows an axial view from below of the bone fixation element according to FIG. 5. The bone fixation element shown in FIGS. 1-4 essentially consists of a head end 1, a shaft part 3 provided with a thread 2 and a front part 4 with a tip 5. The bone fixation element also has a longitudinal axis 7.
Der Vorderteil 4 ist als selbstschneidender, selbstbohrender, zweilippiger Spiralbohrer 11 ausgebildet, dessen Aussen- durchmesser d kleiner ist als der Kerndurchmesser D des Gewindes 2, welches sich bis in den Vorderteil 4 hinein erstreckt. Das Vorderteil 4 weist je nach Gesamtlänge des Knochenfixationselementes eine Länge von 7 - 9 mm auf. Das Kopfende 1 ist - wie in Fig. 2 dargestellt - mit einer zentralen Vertiefung 6, in Form eines Innensechskantes, versehen, welche zur Aufnahme eines Eindrehinstrumentes dient. Das Kopfende l weist im weiteren einen transversal zur Längsachse 7 verlaufenden Kanal in Form einer Durchgangsbohrung 8 auf, welch die Längsachse 7 senkrecht schneidet. Der Durchmesser der Durchgangsbohrung 8 sollte etwa 35 - 50 %, vorzugsweise 39 - 44 % des Durchmessers des Kopfendes 1 oder des Schaftteils 3 betragen.The front part 4 is designed as a self-tapping, self-drilling, double-lip twist drill 11, whose outer diameter d is smaller than the core diameter D of the thread 2, which extends into the front part 4. Depending on the total length of the bone fixation element, the front part 4 has a length of 7-9 mm. The head end 1 is - as shown in Fig. 2 - provided with a central recess 6, in the form of a hexagon socket, which serves to hold an insertion tool. The head end 1 furthermore has a channel running transversely to the longitudinal axis 7 in the form of a through hole 8, which intersects the longitudinal axis 7 perpendicularly. The diameter of the through bore 8 should be approximately 35-50%, preferably 39-44% of the diameter of the head end 1 or of the shaft part 3.
Die Durchgangsbohrung 8 dient dazu einen Faden oder einen Draht aufzunehmen mit welchem entweder mehrere Knochen- fixationselemente untereinander verbunden werden können oder weitere osteosynthetische Elemente oder anatomische Strukturen am Knochen verankert werden können. Wie in Fig. l gezeigt kann das Knochenfixationselement, zusätzlich zur Durchgangsbohrung 8 (oder auch stattdessen) , mit einer an der Aussenseite 9 des Kopfendes l peripher verlaufenden Aussennute 10 versehen sein, welche koaxial zur Längsachse 7 verläuft. Die Aussennute 10 dient dem gleichen Zweck wie die Durchgangsbohrung 8, d.h. zur Aufnahme eines Fadens oder Drahtes.The through hole 8 serves to receive a thread or a wire with which either several bone fixation elements can be connected to one another or further osteosynthetic elements or anatomical structures can be anchored to the bone. As shown in FIG. 1, in addition to the through hole 8 (or instead), the bone fixation element can be provided with an outer groove 10 which runs peripherally on the outside 9 of the head end 1 and which runs coaxially to the longitudinal axis 7. The outer groove 10 serves the same purpose as the through hole 8, ie for receiving a thread or wire.
Bei einer in den Fig. 5 - 8 dargestellten alternativen Ausführungsform eines im übrigen zu den Fig. l - 4 analogen Knochenfixationselementes ist die Durchgangsbohrung 8 als nach oben offener Schlitz ausgebildet. Zudem ist die Durchgangsbohrung 8, wie in Fig. 5 dargestellt, statt im Kopfende 1 im Schaftteil 3 angeordnet, welcher bei dieser Ausführungsform keine Aussennut trägt.In an alternative embodiment shown in FIGS. 5-8 of a bone fixation element which is otherwise analogous to FIGS. 1-4, the through bore 8 is designed as a slot which is open at the top. In addition, the through hole 8, as shown in FIG. 5, is arranged in the shaft part 3 instead of in the head end 1, which in this embodiment has no external groove.
Wie in Fig. 6 gezeigt, weist das Kopfende 1 einen Kreuzschlitz 12 auf, welcher zur Aufnahme eines Eindrehinstrumentes, insbesondere eines Schraubenziehers dient.As shown in FIG. 6, the head end 1 has a cross slot 12, which is used to hold an insertion tool, in particular a screwdriver.
Die erfindungsgemässen Knochenfixationselemente können vom Chirurgen direkt, d.h. ohne Vorbohrung, mittels eines geeigneten Eindrehinstrumentes, z. B. einem Sechskant, oder Kreuzschlitz-Schraubenziehers in den Knochen gedreht werden. The bone fixation elements according to the invention can be carried out directly by the surgeon, i.e. without pre-drilling, using a suitable insertion tool, e.g. B. a hexagon, or Phillips screwdriver in the bone.

Claims

Patentansprüche claims
l. Knochenfixationselement mit einer Längsachse (7), einem Kopfende (1) , einem mindestens teilweise mit einem Gewinde (2) versehenen Schaftteil (3) sowie einem Vorderteil (4) mit Spitze (5) , dadurch gekennzeichnet, dassl. Bone fixation element with a longitudinal axis (7), a head end (1), an at least partially with a thread (2) provided shaft part (3) and a front part (4) with tip (5), characterized in that
A) der Vorderteil (4) als Bohrer ausgebildet ist; undA) the front part (4) is designed as a drill; and
B) das Kopfende (1) oder der Schaftteil (3) mit einem transversal zur Längsachse (7) verlaufenden Kanal (8,10) versehen ist, zur Aufnahme eines Fadens oder Drahtes.B) the head end (1) or the shaft part (3) is provided with a channel (8, 10) running transversely to the longitudinal axis (7), for receiving a thread or wire.
2. Knochenfixationselement nach Anspruch l , dadurch gekenn¬ zeichnet, dass der als Bohrer ausgebildete Vorderteil (4) selbstbohrend und selbstschneidend ist.2. Bone fixation element according to claim 1, characterized in that the front part (4) designed as a drill is self-drilling and self-tapping.
3. Knochenfixationselement nach Anspruch 1 oder 2, dadurch gekennzeichnet, dass der als Bohrer ausgebildete Vorderteil (4) einen maximalen Aussendurchmesser d aufweist, welcher höchstens so gross ist als der Kerndurchmesser D des Gewindes (2) .3. Bone fixation element according to claim 1 or 2, characterized in that the front part (4) designed as a drill has a maximum outer diameter d which is at most as large as the core diameter D of the thread (2).
4. Knochenfixationselement nach einem der Ansprüche 1 - 3, dadurch gekennzeichnet, dass der Vorderteil (4) als Spiralbohrer ausgebildet ist.4. Bone fixation element according to one of claims 1-3, characterized in that the front part (4) is designed as a twist drill.
5. Knochenfixationselement nach einem der Ansprüche 1 - 4, dadurch gekennzeichnet, dass der Vorderteil (4) als zweilippiger Bohrer ausgebildet ist. 5. Bone fixation element according to one of claims 1-4, characterized in that the front part (4) is designed as a two-lip drill.
6. Knochenfixationselement nach einem der Ansprüche 1 bis 5, dadurch gekennzeichnet, dass der Vorderteil (4) eine Länge von 3 bis 18 mm, vorzugsweise von 4 bis 12 mm, aufweist.6. Bone fixation element according to one of claims 1 to 5, characterized in that the front part (4) has a length of 3 to 18 mm, preferably from 4 to 12 mm.
7. Knochenfixationselement nach einem der Ansprüche l bis 6, dadurch gekennzeichnet, dass sich das Gewinde (2) bis in den Vorderteil (4) hinein erstreckt.7. Bone fixation element according to one of claims 1 to 6, characterized in that the thread (2) extends into the front part (4).
8. Knochenfixationselement nach einem der Ansprüche 1 bis 7, dadurch gekennzeichnet, dass das Kopfende (1) mit einer zentralen Vertiefung (6), vorzugsweise einem Innensechskant, zur Aufnahme eines Eindrehinstrumentes versehen ist.8. Bone fixation element according to one of claims 1 to 7, characterized in that the head end (1) is provided with a central recess (6), preferably a hexagon socket, for receiving an insertion tool.
9. Knochenfixationselement nach einem der Ansprüche 1 bis 8, dadurch gekennzeichnet, dass der Kanal (8,10) eine Durchgangsbohrung (8) ist, welche vorzugsweise die Längsachse9. Bone fixation element according to one of claims 1 to 8, characterized in that the channel (8,10) is a through hole (8), which is preferably the longitudinal axis
(7) schneidet.(7) cuts.
10. Knochenfixationselement nach Anspruch 9, dadurch gekennzeichnet, dass der Durchmesser der Durchgangsbohrung (8) 35 - 50 %, vorzugsweise 39 - 44 % des Durchmessers des Kopfendes (1) oder des Schaftteil (3) beträgt.10. Bone fixation element according to claim 9, characterized in that the diameter of the through hole (8) is 35-50%, preferably 39-44% of the diameter of the head end (1) or the shaft part (3).
11. Knochenfixationselement nach einem der Ansprüche 1 bis 10, dadurch gekennzeichnet, dass der Kanal (8,10) eine an der Aussenseite (9) des Kopfendes (1) peripher verlaufende Aussennute (10) ist, welche vorzugsweise koaxial zur Längsachse11. Bone fixation element according to one of claims 1 to 10, characterized in that the channel (8,10) on the outside (9) of the head end (1) is peripheral groove (10), which is preferably coaxial to the longitudinal axis
(7) verläuft. (7) runs.
12. Knochenfixationselement nach einem der Ansprüche 1 bis 11, dadurch gekennzeichnet, dass sie einen im Kanal (8,10) eingeführten Faden oder Draht aufweist. 12. Bone fixation element according to one of claims 1 to 11, characterized in that it has a thread or wire inserted in the channel (8, 10).
PCT/CH1996/000210 1995-06-13 1996-06-04 Self-drilling bone securing component WO1996041573A1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CH1739/95-3 1995-06-13
CH173995 1995-06-13

Publications (1)

Publication Number Publication Date
WO1996041573A1 true WO1996041573A1 (en) 1996-12-27

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2759282A1 (en) * 1997-02-10 1998-08-14 Eos Medical SCREWABLE SCREW DEVICE FOR OSTEOSYNTHESIS PLATE OR FOR COAPTATION OF TWO BONE FRAGMENTS
DE29717413U1 (en) * 1997-09-30 1999-02-04 Degima Medizinprodukte Dr Dr T Thread anchor made of resorbable plastic
FR2770764A1 (en) * 1997-11-07 1999-05-14 Fixano Bone fixing screw for surgery
WO1999039653A1 (en) 1998-02-05 1999-08-12 Institut Straumann Ag Endo-osseal dental implant with a self-cutting screw
EP1260182A2 (en) * 2001-05-17 2002-11-27 Ethicon, Inc. Threaded suture anchor

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2388482A (en) * 1943-01-16 1945-11-06 Herbert H Haynes Surgical screw
US4632100A (en) * 1985-08-29 1986-12-30 Marlowe E. Goble Suture anchor assembly
EP0361756A1 (en) * 1988-09-19 1990-04-04 E. Marlowe Goble Apparatus and procedure for verifying isometric ligament positioning
EP0498709A1 (en) * 1991-02-05 1992-08-12 SCIENCE ET MEDECINE (Société anonyme) Implant for bone surgery for intervertebral stabliser
US5370662A (en) * 1993-06-23 1994-12-06 Kevin R. Stone Suture anchor assembly
EP0657142A1 (en) * 1993-12-07 1995-06-14 Synthes AG, Chur Element for osteosynthesis

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2388482A (en) * 1943-01-16 1945-11-06 Herbert H Haynes Surgical screw
US4632100A (en) * 1985-08-29 1986-12-30 Marlowe E. Goble Suture anchor assembly
EP0361756A1 (en) * 1988-09-19 1990-04-04 E. Marlowe Goble Apparatus and procedure for verifying isometric ligament positioning
EP0498709A1 (en) * 1991-02-05 1992-08-12 SCIENCE ET MEDECINE (Société anonyme) Implant for bone surgery for intervertebral stabliser
US5370662A (en) * 1993-06-23 1994-12-06 Kevin R. Stone Suture anchor assembly
EP0657142A1 (en) * 1993-12-07 1995-06-14 Synthes AG, Chur Element for osteosynthesis

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2759282A1 (en) * 1997-02-10 1998-08-14 Eos Medical SCREWABLE SCREW DEVICE FOR OSTEOSYNTHESIS PLATE OR FOR COAPTATION OF TWO BONE FRAGMENTS
DE29717413U1 (en) * 1997-09-30 1999-02-04 Degima Medizinprodukte Dr Dr T Thread anchor made of resorbable plastic
FR2770764A1 (en) * 1997-11-07 1999-05-14 Fixano Bone fixing screw for surgery
WO1999039653A1 (en) 1998-02-05 1999-08-12 Institut Straumann Ag Endo-osseal dental implant with a self-cutting screw
EP1260182A2 (en) * 2001-05-17 2002-11-27 Ethicon, Inc. Threaded suture anchor
EP1260182A3 (en) * 2001-05-17 2003-08-13 Ethicon, Inc. Threaded suture anchor

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