An elongate element for transmitting forces

Abstract: A hollow elongate element (2) of elastic material for transmitting forces in which the wall (4) comprises openings (6) which reduce the bending resistance moment and are arranged such that the torsion resistance moment of the element essentially remains.

Description: The invention relates to an elongate element for transmitting forces, according to claims 1 and 2. In mechanics as is known elements are used for force transmission whose structure, shape and mounting, in addition to force transmission also effect "flexibility" (elastic deformability) in various combinations of the spacial degrees of freedom. For example a cable transmits tensile force (as a rubber cable or rubber band in an elastic manner) but not compressive force, transverse force, torsion and bending moments. A rigid beam on the other hand transmits all known forces and moments, but however with respect to the cable does not for example offer the free deformability transversely to the extension direction, thus offer e.g. the possibility of changing the transmitted tensile force in its direction by way of redirecting via a roller. Elongate elements for transmitting forces in technical systems are used in a static or dynamic function: a shaft for example is per se a rotating, thus dynamically applied elongate element for transmitting torsional force. The already mentioned beam as part of a rod framework, for example in a scaffolding, is a statically applied elongate element which in particular tensile and compressive force, but also accommodates bending moments in order to prevent buckling. Known elongate elements for transmitting forces in various spacial directions are essentially completely rigid or "slack", but only in a few embodiment forms are of a certain desired flexibility or elasticity (stiffness). Examples of this are the rubber cable already mentioned, which in its longitudinal direction has a certain rubber elasticity and in all other directions is slack. A further example is a so-called bending shaft which elastically accommodates bending moments about any axis perpendicular to its longitudinal axis and transmits torsion force about its longitudinal axis essentially rigidly. Bendable shafts are usually wound from wire and may be coated in order to keep the wire winding in its shape. In order to transmit torsional forces in both directions, it usually requires second oppositely wound wire layers. Such bendable shafts are accordingly manufactured from several parts, but are therefore expensive in their manufacture and furthermore are of a relatively small load capacity and life expectancy. It is the object of the present invention to provide an elongate element for transmitting forces which is elastically bendable perpendicular to its longitudinal axis at least about one axis, and which is improved with respect to its technical characteristics. This object is achieved in the present invention by the features formulated in claims 1 and 2, which concern an implant for a marrow nailing of the upper arm and a shaft for a marrow space drill, respectively. With the present invention this hollow elongate element for transmitting forces is of elastic material. The wall of the elongate element comprises openings in an arrangement which reduce the bending resistance moment of the element. The openings in the wall of the element are arranged such that the torsion resistance moment of the element remains essentially unchanged. The element is tubular. It permits as a one-piece design element a simple manufacture. It requires no lubrication or regular maintenance since there are no different parts which are mounted to one another or rub against one another. The openings are arranged in a pattern recurrent in the longitudinal direction of the element. This is preferably spiral-shaped. The embodiment according to the invention provides slots as openings which in each case extend transversally into the elongate element. The element with a tubular cross section is transversally notched by each slot, wherein a region near to the edge of each notched cross section is not cut through by the slot. The slots are so displaced in the circumferential direction that the regions which are not cut through are arranged in the longitudinal direction of the element in a helical manner. In this manner the bending resistance moment of the element firstly is in each individually notched segment considerably reduced in that each slot does not cut through only one web of the tube walling. The width of the slot dependent of the depth of the slot is formed larger than the tubular wall thickness. The bending resistance moment of the element about this web of a larger width than height is smallest about that axis which lies parallel to the width of the web. Because of this directional dependence of the lowest bending resistance moment of the slotted cross sections and their spiral-shaped arrangement in the longitudinal direction of the element, in the region of a rotation of the helix about the element in each bending direction there is in each case a cross section with a small bending resistance moment. By way of the fact that the helical-shaped pattern is arranged several times about the element in the longitudinal direction of the element, the element is as a whole bendable in every direction. With each torsion-loaded component the principle tension lines run spiral-shaped about the torsional axis. By way of the fact that the openings are arranged in a pattern helical-shaped in the longitudinal direction of the element, also the webs which have not been cut through are arranged helical-shaped and form a helical-shaped uninterrupted material region which is in the position of transmitting principle torsional tensions without being weakened. The element preferably consists of a metallic material. Due to the variety of application possibilities in surgical technology, for example as an implant for the marrow nailing of the upper arm or as a bendable shaft for a marrow space drill, the element preferably consists of biocompatible material, in particular implant steel or titanium. Tension and compressive forces can be transmitted essentially rigidly on account of the one-pieced form of the element. By way of the dimensioning of the openings, in particular by the depth of the slots with the previously described embodiment form, the safety of the element against buckling may be set. Embodiment forms of the invention are hereinafter described in more detail by way of the attached drawings. Fig. 1 shows a lateral view of a cutout of an element for transmitting forces according to the invention. Fig. 2 shows a lateral view of a cutout of a further element for transmitting forces. Fig. 3 shows a section along the line X-Y through the elements in Fig. 1 and 2. In Figs. 1 and 2 the same details or details corresponding to one another are indicated with the same reference numerals. With reference to Figs. 1 and 2 an elongate element 2 for transmitting forces is formed as a tube with a tube outer diameter D and a tube thickness S. The walling 4 of the element 2 comprises slots 6 which with a width B and a depth T in each case transversally extend into the element 2. With this each slot 6 leaves a region 8 of the element, near to the edge, which is not cut through in the respective transversal cross section. The slots 6 are arranged next to one another at a distance to one another. In Fig. 1 each slot 6 is formed displaced to the neighbouring slot at an angle of 90° about the longitudinal axis 10 of the tube. In Figure 2 the angle is 180°. By way of this the element 2 according to Fig. 1 is bendable about two axes which lie at right angles to the longitudinal axis 10 ot the element 2 as well as at right angles to one another. The element 2 according to Fig. 2 is only bendable about one axis which lies at right angles to the longitudinal axis 10 of element 2. Both elements 2 according to Fig. 1 and 2 are for example the implant for bone marrow nailing the upper arm in that on introduction into the drilled out marrow space of the upper arm bone it may follow the curvature of this bone, which is determined by the anatomy. In order to transmit torsional, tensile and compressive force and to be bending-elastic in bending axes perpendicular to the longitudinal axis, the element 2 may be proportioned as follows: the slots 6 have a distance A to one another of >5% and <40% of the tube outer diameter D. The slots 6 have a width B of >20% and <80% of the distance A to the neighbouring slot. The slots 6 are displaced to the neighbouring slot about an angle >20° and ≤180° about the longitudinal axis 10 of the tube. Each slot 6 extends with a depth T of <90% of the tube outer diameter D transversally into the element 2. The wall thickness S of the tubular element 2 is >5% of the tube outer diameter D.

Claims: Implant for the marrow nailing of the upper arm comprising a hollow elongate element (2) for transmitting forces wherein the wall (4) comprises: slots (6) which each extend transversally into the element (2) and of which each slot does not cut through a region (8) of the element which is near to the edge, in the respective transversal cross section, the slots are formed offset to one another and are arranged in a pattern recurrent in the longitudinal direction of the element (2); wherein the element (2) is tubular and wherein each slot is formed to the neighbouring slot at a distance (A) of > 5% and < 40% of the tube outer diameter (D) and with a width (B) of > 20% and < 80% of the distance (A) to the neighbouring slot and wherein each slot extends transversally into the element (2) with a depth (T) of < 90% of the tube outer diameter (D), characterized in that the element has a tube wall thickness (S) > 5% of the tube outer diameter (D) and the slots (6) are arranged in a pattern helical-shaped in the longitudinal direction of the element. Shaft for a marrow space drill comprising a hollow elongate element (2) for transmitting forces wherein the wall (4) comprises: slots (6) which each extend transversally into the element (2) and of which each slot does not cut through a region (8) of the element which is near to the edge, in the respective transversal cross section, the slots are formed offset to one another and are arranged in a pattern recurrent in the longitudinal direction of the element (2); wherein the element (2) is tubular and wherein each slot is formed to the neighbouring slot at a distance (A) of > 5% and < 40% of the tube outer diameter (D) and with a width (B) of > 20% and < 80% of the distance (A) to the neighbouring slot and wherein each slot extends transversally into the element (2) with a depth (T) of < 90% of the tube outer diameter (D), characterized in that the element has a tube wall thickness (S) > 5% of the tube outer diameter (D) and the slots (6) are arranged in a pattern helical-shaped in the longitudinal direction of the element. Implant or shaft according to one of the above claims, wherein the element (2) consists of a metallic material. Implant or shaft according to any of the above claims, wherein the element (2) consists of a biocompatible material, in particular implant steel or titanium. Implant or shaft according to any of the above claims, wherein the slots (6) are arranged about an angle > 20 and ≤ 180° about the longitudinal axis (10) of the tube.

Inventors: HARDER HANS ERICH, JENSEN HARM-IVEN, SPEITLING ANDREAS WERNER DR-IN, HARDER, HANS ERICH, JENSEN, HARM-IVEN, SPEITLING, ANDREAS WERNER, DR.-ING.
Applicants: STRYKER TRAUMA GMBH
Application year: 1998
Main classification: F16C1
IPC codes: A61B17