Medical device, apparatus, and surgical method

Abstract

A medical that is implantable into a human or animal body or being an augmentation device for strengthening human or animal hard tissue for subsequent implantation of a separate implant. The device includes a sheath element suitable of being brought into contact, during a surgical operation, with live hard tissue and/or with hard tissue replacement material. The sheath element has a, for example, generally elongate shape and a longitudinal bore defining a longitudinal opening reaching from a proximal end of the sheath element into a distal direction, and a plurality of holes in a wall of the opening. Further, the device includes a liquefiable element that is insertable or inserted in the longitudinal opening and at least partly liquefiable by the impact of energy impinging from the proximal side.

Claims

1. A medical device, comprising at least a first distinct element and a second distinct element: the first distinct element being an anchor element suitable of being brought into contact, during a surgical operation, with live hard tissue and/or with hard tissue replacement material, the anchor element having a longitudinal opening reaching from a proximal end of the anchor element into a distal direction, and a plurality of holes in a wall of the longitudinal opening; and the second distinct element being a liquefiable element that is insertable or inserted in the longitudinal opening and at least partly liquefiable by the impact of energy impinging from a proximal side so that liquefied material flows through the holes in the wall and out of the longitudinal opening into structures of the hard tissue and/or hard tissue replacement material; wherein the anchor element consists of a material that does not melt at a melting temperature of the liquefiable material of the liquefiable element; wherein the longitudinal opening extends along an axis; wherein the device forms a proximally facing stop face at a distal bottom of the longitudinal opening or of a liquefiable element receiving section thereof where liquefaction of the liquefiable element takes place at said stop face; wherein the proximally facing stop face closes off the longitudinal opening towards a distal side of the longitudinal opening, or at least substantially reduces a cross section of a distal portion of the longitudinal opening compared to a cross section of a proximal portion of the longitudinal opening; wherein the proximally facing stop face is shaped so that it is not rotationally symmetric about the axis such that a cross-sectional shape of the stop face varies as a function of an angle of rotation around the axis; whereby a directing structure is formed by the proximally facing stop face, wherein when the liquefiable element is pressed into a distal direction against the proximally facing stop face while the energy impinges, the stop face acts to first separate the liquefiable material into different portions during movement of the liquefiable material in the distal direction, and only thereafter laterally directs the different portions of the liquefiable material to different ones of the holes.

2. The medical device according to claim 1, wherein the stop face is a proximal end face of a directing structure body terminating the longitudinal opening distally.

3. The medical device according to claim 2, comprising walls that protrude proximally from the directing structure body and extend radially toward an inner surface of the longitudinal opening.

4. The medical device according to claim 2, wherein the directing structure body is a body of the anchor element and is one-piece with the wall of the opening.

5. The medical device according to claim 2, wherein the directing structure body is a body of an insert element insertable in the longitudinal opening, wherein an inner surface of the longitudinal bore comprises a stop structure limiting a movement of the insert element towards distal directions.

6. The medical device according to claim 1, wherein the anchor element is a cannulated surgical screw.

7. The medical device according to claim 6, wherein the cannulated surgical screw is a pedicle anchor for being implanted in a human or animal vertebra from a generally dorsal direction, through one of the pedicles of the vertebra so that a distal portion of the anchor device protrudes into the vertebral body of the vertebra, the pedicle anchor device comprising a proximal head portion for securing an orthopaedic device for stabilizing the spinal column, and comprising a distal shaft portion capable of being anchored in the vertebra, the longitudinal opening reaching from the proximal head portion into the shaft portion.

8. The medical device according to claim 7, the cannulated surgical screw comprising a thread, wherein an outer diameter of the thread is constant and an inner diameter of the thread varies as a function of an axial position, the inner diameter being larger at more proximal positions and smaller at more distal positions.

9. The medical device according to claim 1, comprising a distal axial hole extending distally from the stop face.

10. The medical device according to claim 1, wherein the liquefiable element is configured to be liquefied by the impact of mechanical vibration energy.

11. The medical device according to claim 1, wherein the liquefiable element is configured to be liquefied by the impact of electromagnetic radiation energy.

12. The medical device according to claim 11, wherein the radiation energy is laser radiation energy.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) In the following, ways to carry out the invention and embodiments are described referring to drawings. The drawings mostly are schematical. In the drawings, same reference numerals refer to same or analogous elements. The drawings show:

(2) FIG. 1a is an embodiment of an implant or augmentation device;

(3) FIG. 1b is an embodiment of an implant or augmentation device;

(4) FIG. 1c is a distal portion of a variant of the embodiment of FIGS. 1a and 1 b;

(5) FIG. 1d is a distal portion of a variant of the embodiment of FIGS. 1a and 1b;

(6) FIG. 2 a cross section through the device of FIGS. 1a and 1b during the implantation or augmentation process;

(7) FIG. 3 is an embodiment of a sheath element of an implant or augmentation device;

(8) FIG. 4 is an embodiment of a sheath element of an implant or augmentation device;

(9) FIG. 5 is an embodiment of a sheath element of an implant or augmentation device;

(10) FIG. 6 is a detail of a further embodiment of an implant or augmentation device;

(11) FIG. 7 is a view of an insert element of the implant or augmentation device of FIG. 6;

(12) FIG. 8 is a further embodiment of a sheath element;

(13) FIG. 9 is a further embodiment of a sheath element;

(14) FIG. 10 a pedicle screw being an even further embodiment of a sheath element and being an embodiment of a pedicle anchor device;

(15) FIG. 11 a pedicle screw being an even further embodiment of a sheath element and being an embodiment of a pedicle anchor device;

(16) FIG. 12 a pedicle screw being an even further embodiment of a sheath element and being an embodiment of a pedicle anchor device.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

(17) The device schematically depicted in FIGS. 1a and 1b may be a surgical implant, for example for being anchored in hard tissue and/or hard tissue replacement material. It may have a function similar to the function of a surgical screw, and/or of an anchor (such as a suture anchor or an implant to which a dental crown is to be mounted), or it may have a “standalone” function, for example by containing a substance to be delivered to a surrounding tissue, and/or by containing a different device such as an electronic device, etc. Like in all other embodiments of the invention, the device, if being designed to remain in the patient's body after surgical operation, may have any function a surgical device anchored in hard tissue and/or hard tissue replacement material may have in surgery. As an alternative to being designed to remain the patient's body after the surgical operation, the devices according to the different embodiments—unless explicitly stated otherwise—may also be a temporary anchor or may be an augmentation device, for example as taught hereinafter.

(18) The device 1 is insertable into an opening or a gap or the like of hard tissue and/or hard tissue replacement material, essentially by a movement along an implantation axis 3 that is also considered to be a longitudinal axis of the device. The device comprises a sheath element 11 with a proximal wall portion 11.1 that surrounds a longitudinal bore 13 open to the proximal side of the sheath element. A distal end portion 11.2 terminates the longitudinal bore distally. The distal end portion forms the directing structure. The directing structure comprises a ramp portion 12 sloping away in a concave manner from a center around the longitudinal axis. At the radially outer side of the ramp portion, the wall portion of the sheath element has four holes 14 equally distributed around the circumference of the sheath element. At angular positions between the holes, the directing structure further comprises walls 15 angularly sub-dividing a portion of the longitudinal bore volume communicating with the holes 14. In the depicted embodiment, the walls don't have constant thickness and taper towards a proximal edge 15.1.

(19) The device further comprises a liquefiable element 21, namely a polymer pin 21 that is adapted to the sheath element to be inserted in the longitudinal bore 13 from the proximal side.

(20) For the anchoring or augmenting process, the liquefiable element 21 is inserted and brought into a position where it abuts against the directing structure. More precisely, the liquefiable element 21 abuts against the stop face 20, which, for example, consists of the elements show in FIG. 1b that are within the wall of the sheath element 11 (i.e., walls 15, proximal edge 15.1, and ramp portion 12). While the sheath element is in contact with hard tissue and/or hard tissue replacement material 31, the liquefiable element is pressed against the directing structure, in particular against the stop face 20, while energy impinges from the proximal side. Under the additional effect of the pressing force, the liquefied material of the liquefiable element is pressed out through the holes 14 and into structures, like pores, surface unevenness, inhomogeneities etc. of the hard tissue and/or hard tissue replacement material 31.

(21) The variant of the sheath element depicted in FIGS. 1c and 1d is distinct from the above-described embodiment by the following features.

(22) a. Instead of four holes 14 along the circumferential wall, only two such holes 14 are present. The directing structure is shaped accordingly. If the directing structure is symmetric, the symmetry of the directing structure is therefore two-fold instead of four-fold as in FIGS. 1a, 1b.

(23) b. The ramp portion 12 of the directing structure is not concave but approximately plane.

(24) c. The holes 14 are not circular or approximately circular but elongate; in the depicted embodiment the axial extension is substantially larger than the extension along the circumferential direction.

(25) d. The directing structure comprises an additional, distal, axial hole 19. A first potential advantage of such a distal hole is guidance. During surgery, a thin element such as a so-called Kirschner wire (K wire) can be directed to the target location, and a distal end may be provisionally fixed there. The sheath element may then be positioned by sliding to the target location on the thin element, whereafter the thin element may be removed. A second potential advantage is an additional distal fixation by liquefiable, liquefied material being pressed out of the distal hole 19, too, and being pressed into structures of the tissue around the exit of the distal hole.

(26) All of these features may be present in combination (as depicted in FIGS. 1c and 1d) or alone (for example, the structure of FIGS. 1a, 1b may be provided with a distal hole 19 with the four holes and the directing structure remaining as they are, etc.). They may also be incorporated in any sub-combination (for example, the structure of FIGS. 1a, 1b may be modified to comprise two holes and a two-fold symmetry, an additional distal hole, but with the concave directing structure and an approximately circular hole shape, etc.

(27) The additional distal hole 19 (if present) may be engineered to serve for pressing out liquefied material or not, depending on the requirements. As a rule, the larger the diameter and the smaller the depth, the more is there a tendency for the liquefied material to be pressed out. Also the amount of sheath element material around the distal hole 19 that participates in cooling the material within the distal hole plays a role. In a sheath element of the kind illustrated in FIG. 1c and made of Titanium, a PLDLA pin has been used as a liquefiable element. In a distal hole 19 of a diameter of 1.7 mm and a length of 3 mm, small amounts of liquefied material have been observed to exit through the distal hole in some experiments, whereas in other experiments the material froze in the hole. The ratio d/l of 1.7/3 may thus be viewed as a threshold in implants of this kind. For larger diameters or shorter depths, there is a reliable effect of material exiting through the distal hole, whereas by smaller diameters or substantially larger depths, the outflow may reliably be prevented due to the material freezing in the hole during the process.

(28) While the particular ratio is characteristic of the shape of FIG. 1c, the same principle applies to other shapes.

(29) A distal hole of the kind shown in FIG. 1c is not necessarily cylindrical. Rather, other shapes may be used, including irregular elements protruding from the wall inwards into the distal hole.

(30) If the distal hole is dimensioned to cause material to flow out, but the surgeon does not want material to flow out distally, a simple plug may be used to close off the distal hole.

(31) More in general, a sheath element of embodiments of the invention may comprise any one of or any combination of features a.-d. Instead of feature a., any other number of holes may be present. As illustrated in FIG. 2, an advantageous way of causing energy to impinge is by way of a sonotrode 35 that is pressed against a proximal end face of the liquefiable element while mechanical vibrations are coupled into the sonotrode. The mechanical vibrations are coupled into the liquefiable element 21, and the vibration energy is at least partly absorbed at the interface to the directing structure causing the polymer material of the liquefiable element to at least locally liquefy at this interface. The angular structuring of the directing structure with the walls between the holes firstly has the function to separate portions of the liquefiable element during liquefaction. Due to this, approximately equal amounts of liquefied material is pressed out of every one of the four holes 14, even if the liquefied material while being pressed out of the different holes 14 encounters different resistance. A second function of the walls 15 that protrude distally from the directing structure body and the stop face is that of energy directors. The liquefiable material will have a tendency to start liquefying, under the impact of mechanical vibrations, at edges or other pronounced structures either of the sheath element or of the liquefiable element itself. The energy directing function of the walls 15 is a means for causing the liquefaction to start and take place in vicinity of the holes 14 and not, for example, at the proximal interface to the sonotrode where too early an onset of liquefaction would be undesired.

(32) FIG. 2 illustrates the situation during the anchoring or augmentation process if the sheath element is inserted in a pre-made bore in bone tissue 31. Liquefied and re-solidifying material portions 22 pressed into the surrounding bone tissue 31 and interpenetrating structures of the latter strengthen the tissue that may be cancellous bone or according replacement material. In addition, if the device is an implant meant to remain in the patient's body and portions of the liquefiable material remain, after re-solidifying, in the sheath element, the connection provides a solid anchoring.

(33) FIGS. 3-5 show different views of a further embodiment of a sheath element of a device according to the invention. In addition to the features of the sheath element 11 described referring to FIGS. 1a, 1b, and 2, the sheath element 11 comprises the following features:

(34) e. A collar portion 11.3 that is for example used to fasten a different, not shown element to the hard tissue and/or hard tissue replacement material.

(35) f. The holes 14 have a longer axial (with respect to the longitudinal axis) extension and proximally reach further than the edges 15.1 of the walls 15. The long axial extension is especially suited for devices destined to remain in the patient's body, because they cause a large interface between liquefied material portions interpenetrating the tissue on the one hand and material portions remaining in the sheath element on the other hand.

(36) g. The walls 15 have a portion with a constant thickness ending in the edges 15.1.

(37) h. The ramp portion 12 is not spherical but conical, thus its section with a plane going through the longitudinal axis is a straight line and not concave.

(38) i. The edges 15.1 of the walls 15 slope towards the center.

(39) These features can be realized all in combination (as in the embodiment of FIGS. 3-5) or individually or in any sub-combination, and in any combination with features a.-d., except that features b. and h. both refer to (alternative) ramp portion shapes.

(40) The particular shape of the walls and the ramp portions of the embodiment shown in FIGS. 3-5 features advantages pertaining to the manufacturing of the sheath element. Particularly, it is possible to manufacture the sheath element by adding the longitudinal bore to a pin-shaped blank by drilling and adding, by drilling at an acute angle, the holes 14. In this, the drilling tool may have a conical end portion and may be moved up and down when the holes 14 are made to create their elongate shape. However, the sheath element 11 of FIGS. 3-5, like sheath elements of the other embodiments of this invention, are not restricted to sheath elements made by a particular manufacturing method. Rather, other techniques of manufacturing, including machining techniques and casting techniques, may be used to manufacture the sheath element. The skilled person will know and/or will find an abundance of literature pertaining to the manufacturing of, for example, medical devices of titanium or other metals, ceramics, hard plastics, etc.

(41) FIGS. 6 and 7 show a further embodiment of a medical device. Compared to the previously described embodiments, the embodiment of FIGS. 6 and 7 incorporates the following features:

(42) j. The outer side of the sheath element comprises an outer thread 11.4.

(43) k. The longitudinal bore 13 is a through bore, making the device suitable for being guided by a wire in minimally invasive surgery. The through bore is narrowed towards the distal side so that a shoulder 11.5 is built. The shoulder serves as a stop structure for an insert element 18 that terminates the longitudinal opening for the liquefiable element towards the distal side and that comprises the directing structure including the stop face comprising the walls 15 and the ramp portions 12. The insert element comprises a distal tapered portion 19 that together with the shoulder 11.5 co-operates to form a force fit.

(44) Features j. and k. may be realized alone or in combination, and there is the option to combine with any one of features a.-i.

(45) Other stop structures would be possible. For example the sheath element may comprise at least one interior axial groove that reaches from the proximal end of the sheath element to a distal stop and in which a corresponding number of ridges or tongues of the insert element is guided. Such an embodiment features the additional advantage that the angular relative orientation of the sheath element and the insert element is well-defined during insertion. As an even further variant of a stop structure, the insert element may comprise a spring deflected, during insertion in the sheath element, radially inward against a spring force and forcing a stop flange portion into an annular stop groove of the sheath element at the appropriate axial position. Various other stop structures are possible.

(46) Further features of the embodiment of FIGS. 6 and 7 are:

(47) l. The edges 15.1 of the walls 15 slope towards the center (c.f. feature i.)

(48) m. The walls 15 protrude proximally further than the holes 14. By this, the effect of a controlled distribution of liquefied material between the different holes is effective even if the resistance encountered for liquefied material pressed out of the holes differs strongly between the holes because the interface between liquefied material and still solid material may be expected to be proximal of the upper (most proximal) end of the holes 14 (in contrast to feature f.; feature m. may be combined with any other one of features a.-k).

(49) FIG. 8 depicts an embodiment of a sheath element 11 of the kind described referring to FIGS. 6 and 7 that is a surgical screw, for example a pedicle screw, or an augmentation device that is suitable for preparing an insertion of a surgical screw, as described hereinafter in more detail.

(50) FIG. 9 depicts a section along the plane IX-IX in FIG. 8 illustrating optional features that may be realized in any embodiment, either alone or in combination. The holes 14 are not strictly radial, but axes of the holes, do not go intersect the proximodistal axis. This brings about an asymmetry of the holes with respect to clockwise vs. anticlockwise rotational movements of the device. This in turn produces sharp edges marked by X in FIG. 9. If the device, after the anchoring or augmentation process, is turned in a direction that corresponds to a clockwise rotation in FIG. 9, the liquefied and re-solidified material remaining in the hole is subject to both, a shearing force and a cutting action by the sharp edges X. This will favor a separation between liquefiable material portions outside of the sheath element and interpenetrating the hard tissue and/or hard tissue replacement material on the one hand and liquefiable material portions remaining in the sheath element on the other hand. A configuration where an unscrewing corresponds to a clockwise rotation in FIG. 9 is thus advantageous in cases where the device is an augmentation device, where the sheath element is to be retracted. If, on the other hand, the device after anchoring is turned in a counter-clockwise direction, the force acting on the liquefied and re-solidified material in the holes 14 will have a radial and an axial component, with reduced shearing forces, and no cutting occurs. In such a situation, there will be a strong resistance to a rotational movement. A configuration where an unscrewing corresponds to a counterclockwise rotation in FIG. 9 is thus advantageous in cases where the device is designed to remain anchored in the body of the patient. The holes 14 are not at equal axial positions. Rather, the positions may follow the thread. This feature may be advantageous if the sheath element comprises a thread, although an interruption of the thread—if the holes are at equal axial positions or have another axial position distribution—is in most cases not a problem.

(51) The principle of the outflow holes being asymmetrical with respect to a radial direction may be implemented independent of the described aspect of the invention. It may be used for medical devices comprising a sheath element suitable of being brought into contact, during a surgical operation, with live hard tissue and/or with hard tissue replacement material, which is based on the liquefiable material being inserted (pre-assembled or inserted in situ) in a longitudinal bore of the sheath element and where the sheath element comprises at least one hole in the sheath element wall, through which the liquefied material is pressed from the longitudinal bore into the structures (pores or cavities or other structures) of the bone tissue or other hard tissue or hard tissue replacement material in which anchoring is desired.

(52) The hereinbefore described embodiments may, in addition or as an alternative to the mentioned optional features, be provided in the following variants: Multi-tiered anchoring or augmentation with a plurality of insert elements sequentially inserted, the second, more proximal insert element inserted after anchoring or augmentation with the first, more distal insert element, or with a distal directing structure of the sheath element and with at least one insert element to be placed proximally of the distal directing structure after anchoring with the latter. In this, the sheath element comprises one or more holes for each of the different insert elements or for the distal directing structure and the at least one insert element. The sheath element may comprise a plurality if inner shoulders that have a stepwise reduced cross section towards the distal side, or may comprise different guiding grooves reaching to different distal positions for the different insert elements. The number of holes 14 attributed to a particular directing structure does not need to be four as in the illustrated embodiments but may be two (like in FIGS. 1c and 1d), three, five, six, etc. Also, the angular (azimuthal) spacing does not need to be equal between all holes but may be adapted to a particular situation. For example, for introduction of an implant in a gap of a joint, the sheath element may comprise two pairs of neighboring, relatively close holes at opposite sides. In the case of multi-tiered anchoring, each tear may have an individual number and distribution of holes. The holes may have different shapes and/or different sizes.

(53) The multi-tiered anchoring or augmentation as described herein thus comprises a first liquefaction process taking place with a first directing structure, —of the sheath element or of an initially separate insert element—the subsequent (after an at least partial re-solidification of the liquefied material) addition of a further directing structure of a (second) insert element and then a second liquefaction. This multi-tiered anchoring or augmentation may be applied independent of the aspect of the invention, i.e. also in situations where a directing structure against which the liquefiable material is pressed is not angularly structured.

(54) Referring to FIGS. 10, 11, and 12, a bone screw, namely a pedicle screw 41 based on the first aspect of the invention is depicted.

(55) The pedicle screw 41 comprises a screw head 42, a threaded section 43, and a distal end portion 44. The pedicle screw further comprises a longitudinal through bore 13 that, towards the distal end, comprises a narrowed portion so that a shoulder 11.5 for stopping the insert element (not shown in FIGS. 10-12, the type thereof may for example be similar to the one of the device of FIG. 7) inserted from the proximal side is formed.

(56) The thread has a constant outer diameter (major diameter), whereas a core diameter (minor diameter) is larger at the proximal side than at the distal side. More concretely, in the depicted embodiment, in a central portion of the threaded section the core diameter gradually reduces, whereas in peripheral portions the core diameter is constant. In other, alternative embodiments, the core diameter is constant, is gradually reduced along the entire length of the threaded section, or the core diameter has stepped characteristics as taught in WO 90/02526, or has any other characteristics. Also, the outer diameter of the threaded section need not be constant. Generally, the approach according to aspects of the invention may be combined with any suitable outer thread. Compared to prior art pedicle screws with a longitudinal bore, the bore diameter is comparably large to make insertion of the liquefiable element—that may be a polymer pin—possible. In the depicted embodiment, the bore diameter at the more proximal portion of the threaded section is 3.1 mm and at the distal portion of the threaded section is 2.9 mm, whereas the major diameter is 6.6 mm and the minor diameter is between 4.4 mm and 5.3 mm. The resulting wall strength has proven to be sufficient.

(57) The screw head is flattened and comprises an inner thread that can be used for coupling to an apparatus for automated insertion, as described hereinafter.