Method for the non-invasive fragmentation of residual biomaterial after bone augmentation

Abstract

The invention relates to a method for the non-invasive fragmentation of residual biomaterial after bone augmentation, and to a device specifically adapted for said method.

Claims

1. A method for non-invasive fragmentation of residual biomaterial after bone augmentation, the method comprising: generating shock waves; applying the shock waves transdermally or intraorally; and targeting the shock waves toward the residual biomaterial from the bone augmentation to fragment the residual biomaterial.

2. The method of claim 1, wherein the method is performed after an application in orthopedic surgery including bone augmentation with biomaterials.

3. The method of claim 1, wherein the method is performed after an application in dental implanatology including bone augmentation with biomaterials.

4. The method of claim 2, wherein the application in orthopedic surgery including bone augmentation with biomaterials is a surgery in a spine, a surgery to a tibia head, or a hip revision arthroplasty.

5. The method of claim 1, wherein generating the shock waves comprises generating the shock waves as pulsed shock waves.

6. The method of claim 1, further comprising focusing the shock waves toward the residual biomaterial.

7. The method of claim 3, further comprising applying the shock waves with an appropriately angulated device to target a desired area of an alveolar crest intraorally.

8. The method of claim 7, wherein an angle between a head of a shock wave generator generating the shock waves and a handle of the appropriately angulated device ranges between 25 and 90 degree.

9. The method of claim 1, wherein the residual biomaterial is osteoconductive with an interconnecting porous system.

10. The method of claim 1, wherein the residual biomaterial is resorbable.

11. The method of claim 5, further comprising focusing the pulsed shock waves toward the residual biomaterial.

12. The method of claim 5, further comprising applying the pulsed shock waves with the aid of an appropriately angulated device to target a desired area of the alveolar crest intraorally.

13. The method of claim 5, wherein an angle between a head of a shock wave generator generating the pulsed shock waves and a handle of the appropriately angulated device ranges between 25 and 90 degree.

14. The method of claim 5, wherein the residual biomaterial is osteoconductive with an interconnecting porous system.

15. The method of claim 5, wherein the residual biomaterial is resorbable.

16. The method of claim 5, wherein the pulsed shock waves are applied in fast repetition.

17. The method of claim 5, wherein the pulsed shock waves result in pressures between 30 and 150 MPa for 0.5-3 microseconds, after a rise time of around 10 ns.

18. The method of claim 5, wherein the pulsed shock waves result in pulse energies in a range of 10 to 100 mJ.

19. The method of claim 5, wherein the pulsed shock waves result in energy densities between about 0.2 and 2.0 mJ/mm.sup.2, and wherein energy density is defined as an amount of acoustical energy transmitted through an area of 1 mm.sup.2 per pulse.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) FIG. 1 shows a coronal cut transection of the skull with the maxillary bone and a biomaterial block osseointegrated in the alveolar bone.

(2) FIG. 2 shows a disrupted biomaterial block pieces that will be partly or totally resorbed during the bone healing process.

(3) FIG. 3 shows an optimized result with no residual biomaterial left.

(4) FIG. 4 shows an acoustic lens of a shock wave generator with an adaptor which allows to adjust the focal point/target area of the lens to the position of the target at the implantation site of the biomaterial.

(5) FIG. 5 shows a focused and a radial applicator hand piece with respect and the resulting shock wave width and depth.

(6) FIG. 6 shows schematic representations of three different hand-held shock wave applicators

(7) (a) represents a hand-held shock wave applicator according to the state of the art

(8) (b) represents a hand-held shock wave applicator according to the invention, wherein the shock wave emitting part of said device forms an angle of 25 degree with the rest of the device;

(9) (c) represents a hand-held shock wave applicator according to the invention, wherein the shock wave emitting part of said device forms an angle of 90 degree with the rest of the device;

DETAILED DESCRIPTION OF THE INVENTION

(10) The bone augmentation relates to those applied biomaterial blocks with interconnecting porous system as described above (BIPS).

(11) The related biomaterial blocks are osteoconductive and thus support the bony ingrowth of newly formed bone into the matrix.

(12) The related biomaterial blocks (BIPS) are preferably mineralized bone matrices (MBM), including allogeneic or xenogeneic ones, artificial biomaterial with interconnecting porous system or said biomaterial blocks containing collagen or other proteins or other resorbable biomaterials, including ceramics like tricalcium phosphate and silicates, biopolymers selected from the group consisting of polycaprolactone, polylactides and polysilicates, or chitosan or sugar-polymers.

(13) The related biomaterial blocks alternatively may be non-resorbable BIPSs, including ceramics like hydroxylapatite or xenogenic ceramics or non-resorbable material types of the above mentioned.

(14) The related biomaterial blocks alternatively may be other biomaterials with osteoconductive properties.

(15) The described shock wave application relates to the application of this technology in urology known as Extracorporeal Shock Wave Lithotripsy (ESWL). Shock waves in ESWL have typically a broad frequency spectrum between 20 kHz and some MHz. Most energy is between 100 kHz and 1 MHz with a peak at 300 kHz. Shock waves are typically applied in pulsed dosing to allow a calculated energy application with less heat generation, e.g. US patent application US 2012/0215138 A1 and US patents cited therein. The strong application of a short shock wave leads to mechanical disruption of stiff structures as urea stones and to cavitation effect associated with it. This leads to pressures between 30 and 150 MPa for 0.5-3 microseconds, after a rise time of around 10 ns and a following decompression with a negative pressure peak of approximately −30 MPa over 2-20 microseconds. Pulse energies are in a range of 10 to 100 mJ and energy densities are between about 0.2 and 2.0 mJ/mm.sup.2 whereby energy density is defined as the amount of acoustical energy transmitted through an area of 1 mm.sup.2 per pulse.

(16) Said pulses of shockwaves are applied in fast repetition (short pulse shockwave).

(17) Further embodiments of the present invention are the following methods, wherein:

(18) (A) said method is applied in dental implantology or orthopedic surgery after bone augmentation with biomaterials.

(19) (B) said method is applied in orthopedic surgery after bone augmentation with biomaterials in the spin or the tibia head or after hip revision arthroplasty.

(20) (C) said shock waves are applied in the form of pulsed shock waves.

(21) (D) said shock waves are focused toward said residual biomaterial.

(22) (E) said shock waves are applied with the aid of an appropriately angulated device to target the desired area of the alveolar crest intraorally, in particular wherein the angle between the head of the shock wave generator and the handle ranges between 25 and 90 degree.

(23) (F) the residual biomaterial is osteoconductive with an interconnecting porous system and/or resorbable.

(24) All shock wave devices hitherto known are not suitable for intraoral fragmentation of residual biomaterial after bone augmentation in dental implantology, since non-angulated, linear devices cannot be applied easily intraorally.

(25) Accordingly, the invention also relates to an adapted shock wave generator, which focuses the shock wave on the residual biomaterial after bone augmentation in dental implantology with an angulated applicator appropriate for intraoral application.

(26) The focus can be adjusted within the applicator technically by modifying the acoustic lens, or by using a fixed focus and optionally expandable spacer device that is attached to the applicator tip in order adjust it to the calculated distance to the tissue surface and a calculated focus depth thereby.

(27) Preferably the system according to the invention consists of a base station and an applicator hand piece.

(28) The described treatment, of disrupting biomaterial implants to achieve better resorption, can be applied in orthopedic surgery in an analogous ways with the existing medical devices as described above. The main indications in orthopedic surgery incudes: tibia head fractures, fraktures of the vertebral body in spine surgery and osteoplasty of the femur in hip revision arthropasty and other arthroplasty.

Example 1

(29) A Botiss bonebuilder allogeneic spongiosa block is selected respecting the blood group and possible other types to reduce the risk of host versus graft reactions. The block is implanted in a defect area in the jaws to achieve an appropriate bony bed for dental implants. The block is fixed with osteosynthesis screws or other appropriate fixation devices. It is even possible to use the dental implant itself as described as Giesenhagen ring technique.

(30) After an appropriate bony healing period of 3 to 6 months, the following treatment is applied before implantation and prosthetic loading by opening the restoration to the oral cavity via the marginal sulcus.

(31) Implantation is left out in this treatment path, if the implantation was already done simultaneously with the bone block implantation.

(32) A Storz MP200 ESWL base station with 21 Hz and 5.0 bar pressure is applied using a Storz Falcon applicator hand piece. The Falcon hand piece is a radial applicator “pump gun” leading to a less focused but also less deep penetration of the shock waves with the advantage of a wide radial effect area (cp. FIG. 5 (a)). The transmission tip is placed extra-orally on the skin and pressed firmly onto the cheek of the buccal region for the waves to reach the target area in the upper jaw or pressed firmly onto the cheek in the mandibular region for the waves to reach the mandibular alveolar crest and the desired region there. The same can be applied in the front teeth region through the lips.

Example 2

(33) As in Example 1, but wherein the hand piece is replaced by a focused hand piece like the Storz Sepia hand piece “Sniper gun” (cp. FIG. 5 (b)). This allows more focused shock waves achieving a better depth by reducing/narrowing the effect area.

Example 3

(34) As in Examples 1 or 2, wherein the base station is replaced by the Storz Duolith ST.

Example 4

(35) A big mobile urological ESWL unit like the Storz Modulith SLK or a stationary unit like the Storz Modulith SLX-F2 can also be applied in a similar manner by adjusting the patient accordingly to allow the applicator to reach the desired target region in the jaws.

(36) It may be necessary to apply appropriate analgesia including a possible intubation narcosis.

Example 5

(37) As in any of the Examples 1 to 4, but wherein the hand piece is applied at the tibia or the hip area or the spine and targeted to the region with biomaterial osteoplasty.

(38) The results of the treatments of examples 1 to 4 are shown in the FIGS. 1 to 3.

(39) FIG. 1 shows a coronal cut transection of the skull with the maxillary bone (1) and a biomaterial block (2) osseointegrated in the alveolar bone. Shock waves can be applied transgingival (3) or transdermal (4) through the related spaces, from facial exterior site (5) or from the oral cavity (6).

(40) FIG. 2 shows the disrupted biomaterial block pieces (7) that will be partly or totally resorbed during the bone healing process.

(41) FIG. 3 shows the optimized result with no residual biomaterial left.

(42) FIG. 4 shows an acoustic lens (9) of a shock wave generator with an expandable distance holder (10), which allows the adjustment of the focal point (8) of the lens with the position of the target at the implantation site of the biomaterial (2). The shock waves (13) are focused (14, 15) by the lens (9). The expansion (11) may be effected by pressurizing the fluid within the distance holder (10) via the inlet valve (16). Therefore, the distance between the lens (9) and the tissue (12) can be adjusted, so that the focal point (8) of the shock wave coincidence with the location of the biomaterial (2).

(43) FIG. 5 shows a focused (17) and a radial applicator (18) hand piece with respect and the resulting shock wave width (19) and depth (20).

(44) FIG. 6 shows schematic representations of three different hand-held shock wave applicators:

(45) (a) represents a linear hand-held shock wave applicator (17) according to the state of the art.

(46) (b) represents an angular hand-held shock wave applicator (21) according to the invention, wherein the shock wave (13) emitting part (23) thereof forms an angle of 25 degree with the rest of the device;

(47) (c) represents another angular hand-held shock wave applicator (22) according to the invention, wherein the shock wave (13) emitting part (23) thereof forms an angle of 90 degree with the rest of the device;

(48) The invention is based on the principle that resorbable biomaterial pieces of small size in an area of active acute healing as generated by the application of shock waves leads to a resorption of such particles.

REFERENCES

(49) 1. Sanz M, Vignoletti F. Key aspects on the use of bone substitutes for bone regeneration of edentulous ridges. Dent Mater. 2015; 31:640-647. 2. Esposito M, Grusovin M G, Kwan S, Worthington H V, Coulthard P. Interventions for replacing missing teeth: bone augmentation techniques for dental implant treatment. Cochrane database of systematic reviews. 2008:CD003607. 3. Draenert F G, Huetzen D, Neff A, Mueller W E. Vertical bone augmentation procedures: basics and techniques in dental implantology. Journal of biomedical materials research. Part A. 2014; 102:1605-1613. 4. Fretwurst T, Spanou A, Nelson K, Wein M, Steinberg T, Stricker A. Comparison of four different allogeneic bone grafts for alveolar ridge reconstruction: a preliminary histologic and biochemical analysis. Oral Surg Oral Med Oral Pathol Oral Radiol. 2014; 118:424-431. 5. Zimmermann G, Moghaddam A. Allograft bone matrix versus synthetic bone graft substitutes. Injury. 2011; 42 Suppl 2:S16-21. 6. Draenert G F, Delius M. The mechanically stable steam sterilization of bone grafts. Biomaterials. 2007; 28:1531-1538. 7. Finkemeier C G. Bone-grafting and bone-graft substitutes. Journal of Bone & Joint Surgery America. 2002; 84-A:454-464. 8. Simion M, Nevins M, Rocchietta I, et al. Vertical ridge augmentation using an equine block infused with recombinant human platelet-derived growth factor-BB: a histologic study in a canine model. Int J Periodontics Restorative Dent. 2009; 29:245-255. 9. Muller W E, Wang X, Diehl-Seifert B, et al. Inorganic polymeric phosphate/polyphosphate as an inducer of alkaline phosphatase and a modulator of intracellular Ca2+ level in osteoblasts (SaOS-2 cells) in vitro. Acta Biomaterialia. 2011; 7:2661-2671. 10. Williams D. The continuing evolution of biomaterials. Biomaterials. 2011; 32:1-2. 11. Costello B J, Shah G, Kumta P, Sfeir C S. Regenerative medicine for craniomaxillofacial surgery. Oral Maxillofac Surg Clin North Am. 2010; 22:33-42. 12. Huebsch N, Mooney D J. Inspiration and application in the evolution of biomaterials. Nature. 2009; 462:426-432. 13. Luong-Van E, Grondahl L, Chua K N, Leong K W, Nurcombe V, Cool S M. Controlled release of heparin from poly(epsilon-caprolactone) electrospun fibers. Biomaterials. 2006; 27:2042-2050. 14. Delloye C, Cornu O, Druez V, Barbier O. Bone allografts: What they can offer and what they cannot. J Bone Joint Surg Br. 2007; 89:574-579. 15. Nissan J, Marilena V, Gross O, Mardinger O, Chaushu G. Histomorphometric analysis following augmentation of the posterior mandible using cancellous bone-block allograft. J Biomed Mat Res A. 2011e; 97 A:509-513. 16. Spin-Neto R, Landazuri Del Barrio R A, Pereira L A, Marcantonio R A, Marcantonio E, Marcantonio E, Jr. Clinical similarities and histological diversity comparing fresh frozen onlay bone blocks allografts and autografts in human maxillary reconstruction. Clin Implant Dent Relat Res. 2013; 15:490-497. 17. Khoury F, Hanser T. Mandibular bone block harvesting from the retromolar region: a 10-year prospective clinical study. The International journal of oral & maxillofacial implants. 2015; 30:688-397. 18. Gellrich N C, Held U, Schoen R, Pailing T, Schramm A, Bormann K H. Alveolar zygomatic buttress: A new donor site for limited preimplant augmentation procedures. Journal of Oral & Maxillofacial Surgery. 2007; 65:275-280. 19. Nissan J, Ghelfan O, Mardinger O, Calderon S, Chaushu G. Efficacy of cancellous block allograft augmentation prior to implant placement in the posterior atrophic mandible. Clin Implant Dent Relat Res. 2011a; 13:279-285. 20. Simion M, Jovanovic S A, Tinti C, Benfenati S P. Long-term evaluation of osseointegrated implants inserted at the time or after vertical ridge augmentation. A retrospective study on 123 implants with 1-5 year follow-up. Clin Oral Implants Res. 2001; 12:35-45. 21. Iglhaut G, Schwarz F, Grundel M, Mihatovic I, Becker J, Schliephake H. Shell technique using a rigid resorbable barrier system for localized alveolar ridge augmentation. Clin Oral Implants Res. 2014; 25:e149-154. 22. Schliephake H, Drewes M, Mihatovic I, Schwarz F, Becker J, Iglhaut G. Use of a self-curing resorbable polymer in vertical ridge augmentations—a pilot study in dogs. Clin Oral Implants Res. 2014; 25:435-440. 23. Urban I A, Jovanovic S A, Lozada J L. Vertical ridge augmentation using guided bone regeneration (GBR) in three clinical scenarios prior to implant placement: a retrospective study of 35 patients 12 to 72 months after loading. Int J Oral Maxillofac Implants. 2009; 24:502-510. 24. Delius M, Draenert K, Al Diek Y, Draenert Y. Biological effects of shock waves: in vivo effect of high energy pulses on rabbit bone. Ultrasound Med Biol. 1995; 21:1219-1225.