Biological Mechanisms of Tooth Movement. Группа авторов

Figure 2.19 Behavior of bone during orthodontic tooth movement. The net force, compression, and tension applied by the “leading” edge of the tooth deforms the alveolar bone convexly toward the root. At the “trailing” edge, the periodontal fibers distort the alveolar bone, producing concavity toward the root. Areas that have been described as characterized by osteoblastic activity were electronegative and, conversely, areas of positivity of electrical neutrality were observed in regions characterized by osteoclasia.

      (Source: Zengo et al., 1973. Reproduced with permission of Elsevier.)

Bioelectric signals in orthodontic tooth movement

      In 1957, Fukada and Yasuda published the results of their systematic investigation on dry specimens cut from human and bovine long bones, in an article titled “On the piezoelectric effect of bone,” which credited them with the discovery of the existence of piezoelectricity in bone. They demonstrated that dry bone under proper load application generates surface charges, called piezoelectric currents. They established that the piezoelectric effect appears only when shearing force is applied to the collagen fibers in the bone, which are highly oriented, to make them slip past each other. There exist two types of piezoelectric effects – positive and negative. The former is due to strains generated within the crystal lattice of a material, leading to the production of a potential difference across the faces of that crystal and the latter, when an electric charge is passed across a molecule or crystal and leads to an inherent strain within that molecule (Isaacs, 1987). Both effects involve the organic molecules of collagen and the inorganic crystals of hydroxyapatite (McDonald, 1993). Bassett and Becker (1962) extended that research and discovered that the charges emanating from the bone surface at the time of bending are proportional to the internal strains engendered by the bending. They also showed that the polarization sign always depended upon the type of stress – there was a positive sign where there is tension and a negative sign where there is compression. These experiments were further developed by Shamos et al. (1963) and Shamos and Lavine (1964), who reported finding this phenomenon in a number of different bones, in different anatomical sites and species. They suggested that local electric fields resulting from these surface changes influence the deposition of ions and polarizable molecules.

      The first observations of the piezoelectric phenomenon in wet and living bone was made by Bassett (1968), and this finding has contributed to the working hypothesis that piezoelectricity leads to a physical explanation of Wolff ’s law. Following this discovery, the universal existence of piezoelectricity in biological tissues was demonstrated by Fukada and Hara (1969) through their experiments on trachea, aorta, intestines, ligaments, and venous vessels. Marino and Becker (1975) reported on the piezoelectric characteristics of collagen, and concluded that these effects originate in tropocollagen molecules, or in molecules no larger than 50 Å in diameter. However, the hypothesis claiming that piezoelectricity is a major determinant of bone remodeling is weakened by the following:

      Proffit (2013) outlined two unusual properties of piezoelectricity, which do not seem to correlate well with OTM:

Anderson and Erikkson (1968) challenged the piezoelectric hypothesis and reported that although dry collagen is strongly piezoelectric, full hydrated collagen is not, because of the structured water it contains. They argued that bone is a tissue with high symmetry, as the hydroxyapatite it contains is centrosymmetric in nature, and not piezoelectric. Follow‐up experiments conducted by these investigators (1970), using a similar apparatus to the one used by Fukada and Yasuda in 1957, proved that the piezoelectric coefficients varied with the state of hydration of bone, and that the variation decreased as the specimens were dried by evaporation. The loss of piezoelectricity in fully hydrated tendon collagen was explained as attainment of more symmetrical, nonpiezoelectric structure by absorption of water. Instead, the electrical signals generated when stress is applied to fully wet collagen are actually streaming potentials.

The electrokinetic phenomenon known as streaming potential or streaming current was described by many authors, like Glasstone, Overbeek, and Kortum (Gross and Williams, 1982). Anderson and Eriksson (1968) reintroduced the concept against the theoretical faults of the piezoelectric effect, and reported it to be present in bone as it is a porous tissue containing a fluid phase and calcified matrix (which is composed of inorganic (mainly hydroxyapatite) and organic (collagen) contents). Further, the porosity of bone contains membrane‐lined capillary vessels helping in the transportation of nutrition to the inside of bone. There exists a compartmental model for the bone fluid system whereby extracellular fluid in the calcified matrix is separated from membrane‐lined vascular channels. When the bone is mechanically stressed, as part of different loading conditions, or therapeutically induced as in orthodontic treatment, remodeling changes are initiated by the bioelectric potentials generated from inside of the bone. The presence of bioelectric potentials in bone matrix, which also contains extracellular ionic fluid, will generate a charge separation at the matrix–fluid interface. There will be attraction of opposite‐charged molecules at the matrix–fluid interface and repelling of similar charged molecules away from this interface. When the fluid is forced through a bone plug, the ionic charges in the fluid phase near the fluid–matrix interface are carried towards the low pressure end, which is otherwise known as Poiseuille flow. This flow constitutes the streaming current and accumulation of charges set up as an electrical field. This field will result in generation of conduction currents which flow in opposite directions through the bulk of liquid in the porous structure of bone. In steady state the conduction current is equal to the streaming current. The resulting electrostatic potential difference between these two sides of bone plug is known as streaming potential (Figure 2.20) (Walsh and Guzelsu, 1993). Briefly, streaming potential is the electric potential developed between two components by an electrolyte flowing between the solid surfaces. The movement of the electrostatic double layer at the fluid bone interface, created through the net surface charge gained by the bone surface in contact with an ionic fluid, generates this effect (Anderson and Eriksson, 1968). In bone, streaming potentials can be observed in vascular channels, Haversian systems, canaliculi, and microporosities of the structure due to blood flow and interstitial fluid movement. Neutrality is restored following equilibration of ion distribution.

      Zeta potential, the common link among different electrokinetic potentials and the one used to allow comparison of different measuring techniques, is defined as average potential difference between the bulk and surface of shear. Surface of shear is an imaginary surface present in the area adjacent to electrically charged bone matrix, where the ions and fluid molecules remain stationary. The role of zeta potential is to separate the movement of ions bound to the solid surface