Biomechanical behavior of bone tissue in spine instrumentation.

BACKGROUND: The mechanical fixation of the spine in patients with osteoporotic vertebral degeneration is a challenge for surgeons, the vertebrae selected to insert the screws may fail, endangering health and even patient's life. OBJECTIVE: The objective of the study was to study the effect of the variation of the bone density in the bone-screw interface from a three-dimensional model of the lumbar section. MATERIALS AND METHODS: The finite element method was used to model the behavior of the lumbar vertebral section when applying compression loads. RESULTS: The stresses between 2 and 3 MPa were located on the contact surface with the screw, both in the vertebral body and in the apophysis, being slightly higher in the vertebral body. CONCLUSIONS: Regardless of bone density, the contact zones between the screws are susceptible to bone tissue failure. The posterior half of the vertebral body was the most sensitive to high values of stress, while in the areas furthest from the axis of the screw stress tended to their minimum.

INTRODUCCIÓN: La fijación mecánica de la columna en pacientes con degeneración vertebral osteoporótica es un reto para los cirujanos, pues las vértebras seleccionadas para insertar los tornillos pueden fallar, poniendo en peligro la salud y la vida del paciente. OBJETIVO: Estudiar el efecto de la variación de la densidad ósea en la interfase hueso-tornillo, a partir de un modelo tridimensional de la sección lumbar. MATERIALES Y MÉTODOS: Se emplea el método de los elementos finitos para modelar el comportamiento de la sección vertebral lumbar al aplicar cargas de compresión. RESULTADOS: Los esfuerzos entre 2 y 3 MPa se ubicaron en la superficie de contacto con el tornillo, tanto en el cuerpo vertebral como en la apófisis, siendo ligeramente superiores en el cuerpo vertebral. CONCLUSIONES: Independientemente de la densidad ósea, las zonas de contacto entre el tornillo son susceptibles al fallo del tejido óseo, debido a que están próximos al esfuerzo de fallo óseo de 2.37 ± 1.14 MPa reportado en la literatura. La mitad posterior del cuerpo vertebral fue la más sensible a sufrir valores altos de esfuerzos, mientras que en las zonas más alejadas del eje del tornillo los esfuerzos tendieron a su magnitud mínima.

Analysis and characterization of the normal gait phases of walking Warmblood horses as a tool for the diagnosis of lameness / Análise e caracterização das fases do andamento normal dos cavalos através da combinação de fotogrametria e acelerometria como ferramenta para o diagnóstico da claudicação

Horses with lameness modify gait behavior, but when it is subtle, it may not be possible to identify it clinically. The objective of this research is to characterize the normal gait phases of walking Warmblood horses by combining photogrammetry and accelerometry to monitor lameness to indicate a structural or functional disorder in the extremities. The study was conducted in 23 adult male Warmblood horses. Photogrammetry was used to identify the kinematic variables of the limbs and the markers path over time; triaxial accelerometers were used to capture the orthogonal acceleration components. It was determined that only 10 horses showed a normal gait pattern, there was a 43% correspondence between the expert´s judgment and the diagnostic techniques. According to the Stashak classification of the gait phases, cycle phases to forelimb were 34/4/8/13/41, while for hind limb were 54/11/8/8/19 (% of the stride). The range of motion (ROM) of the neck, knee and fetlock joints was 45.52±5.63°, 196.04±19.7° and 209±11.52° respectively. A combination of experimental methods was used to identify the phases of gait cycle of healthy horses. There was a correspondence in the location of the points of maximum displacement of the limbs with both techniques. More detailed information on the limbs movement was obtained using the accelerometer technology. These methods are applicable to other conditions either outdoors or in the lab.(AU)

Os cavalos com claudicação modificam o comportamento do andamento. Porém, uma leve modificação pode não ser identificada clinicamente. O objetivo desta pesquisa foi caracterizar as fases do andamento normal dos cavalos através da combinação de fotogrametria e acelerometria, para identificar alterações estruturais ou funcionais nos membros. O estudo foi conduzido em 23 cavalos Warmblood machos adultos. A partir da fotogrametria foi possível obter as variáveis cinemáticas das extremidades e a trajetória dos marcadores ao longo do tempo. Por outro lado, os acelerômetros triaxiais foram usados para capturar as componentes ortogonais da aceleração. Determinou-se que apenas 10 cavalos mostraram um padrão de marcha normal, e houve uma correspondência de 43% entre pareceres dos peritos e as técnicas de diagnóstico. De acordo com a classificação das fases da marcha de Stashak, as fases do ciclo da extremidade anterior foram 34/4/8/13/41 enquanto para a extremidade posterior foram 54/11/8/8/19. A amplitude de movimento (ROM) de pescoço, joelho e sesamóide foram 45,52±5,63°, 196,04±19,7° e 209±11,52°, respectivamente. Uma combinação dos métodos experimentais foi utilizada para identificar as fases do ciclo de marcha de cavalos saudáveis. Constatou-se correspondência na localização dos pontos de deslocamento máximo do membro com ambas as técnicas. A informação mais detalhada do movimento dos membros foi obtida usando a acelerometria. Estes métodos são aplicáveis em outras condições, quer a campo ou no laboratório.(AU)

3D patient-specific model of the tibia from CT for orthopedic use.

OBJECTIVES: 3D patient-specific model of the tibia is used to determine the torque needed to initialize the tibial torsion correction. METHODS: The finite elements method is used in the biomechanical modeling of tibia. The geometric model of the tibia is obtained from CT images. The tibia is modeled as an anisotropic material with non-homogeneous mechanical properties. CONCLUSIONS: The maximum stress is located in the shaft of tibia diaphysis. With both meshes are obtained similar results of stresses and displacements. For this patient-specific model, the torque must be greater than 30 Nm to initialize the correction of tibial torsion deformity.