🔍 Key Findings

• Compared unilateral plating (UP) vs orthogonal plating (OP) with 2.0, 2.4, and 3.0 mm plates (OP2.0, OP2.4, OP3.0).
• Model: acetal homopolymer (Delrin) rod with 29 mm fixed fracture gap, loaded axially (4–196 N, 90,000 cycles).
• OP constructs had 2.5–4.1x higher strength and 3.0–4.2x higher stiffness than UP constructs (p < .0002).
• UP had 3.5–4.1x higher gap strain than OP groups (p < .0075).
• All OP groups exceeded 1000 N max load before failure (vs 424 N for UP).
• Greater implant size in OP groups further increased performance.
• All constructs survived fatigue loading; 3.5 mm plates showed deformation, especially UP; OP plates remained intact.

🔍 Key Findings

• 12-hole LCPs (80% plate–bone ratio) showed significantly higher construct stiffness than 6-, 8-, or 10-hole plates in both compression and tension bending.
• Strain on the plate was significantly lower in 12-hole vs 6-hole plates at all regions of interest (ROIs), especially around the fracture gap.
• No incremental increases in stiffness or decreases in strain were observed between 6-, 8-, and 10-hole plates—only when comparing to 12-hole plates.
• Bone model strain adjacent to the plate end was significantly lower for 10- and 12-hole plates vs 6-hole plates under both loading conditions.
• The threshold effect suggests biomechanical benefits only emerge beyond a plate–bone ratio of ~80%.
• Working length increased from 9.4 mm (6-hole) to 13 mm (others), potentially influencing strain/stiffness differences.
• Four-point bending was used, as it replicates the most biomechanically relevant force on plated long bones.
• Clinical implication: Longer plates may reduce plate strain and peri-implant bone strain, potentially lowering risk of fatigue failure or stress risers.

🔍 Key Findings

• Adding a single locking throw significantly increased holding security for specific knots, including the surgeon's throw (p = .0001) and square throw (p = .0002).
• For the Miller's throw (p = .166) and strangle throw (p = .808), no significant improvement was observed with a locking throw.
• After locking throw addition, all five knots leaked at similar pressures (p = .5233), and these pressures exceeded physiologic arterial pressures.
• Surgeon's throw without a locking throw had the lowest leak pressure (62.5 ± 46.2 mm Hg), below physiologic arterial values.
• The square throw without locking also leaked below physiologic pressures (148.7 ± 109.4 mm Hg), though it outperformed the surgeon's throw.
• Miller’s and strangle throws performed significantly better than square or surgeon’s throws without locking, achieving leak pressures >200 mm Hg.
• All knots used 2-0 polyglyconate monofilament (Maxon); no comparisons across suture types or sizes were performed.
• Authors concluded that correct tensioning and locking throw addition are key to safe vascular ligation. Miller’s, strangle, or slip knots are preferred for challenging surgical fields.

🔍 Key Findings Summary

• Primary 3.5-mm LCP used with short (SWL), medium (MWL), and long (LWL) working lengths
• Addition of orthogonal 2.7-mm LCP resulted in:
  • Significantly higher bending stiffness for SWL, MWL, and LWL (p < 0.0001)
  • Higher torsional stiffness for MWL and LWL (not for SWL)
  • Significantly lower strain across all working lengths in bending (p < 0.01)
• Working length inversely related to construct stiffness and directly to plate strain
• Orthogonal plates eliminated stiffness differences across working lengths in bending
• Suggests orthogonal plates can improve implant fatigue life and allow compensation when short working lengths are unachievable

🔍 Key Findings

• Aiming device provided comparable trajectory accuracy to fluoroscopy, especially in right limbs (1.9° vs. 3.4°, p = .0128).
• Eccentricity (deviation from condylar center) was lower with fluoroscopy (3.1 mm vs 4.2 mm, p = .0017), making fluoroscopy more precise.
• Odds of joint infringement were 8× higher with the aiming device, though not statistically significant (p = .0575).
• Residents had greater screw trajectory deviation than diplomates (p = .0366), highlighting impact of experience.
• Aiming device procedures took less time than fluoroscopy in some scenarios, particularly for right limbs with right-handed surgeons.
• Fluoroscopic procedures had more pin/drill attempts, increasing risk of glove puncture and potential aseptic breaks.
• Mean deviation angles in both groups (<3.5°) were within acceptable range to avoid intracondylar fracture gap.
• Cadaver model used large-breed, healthy adult dogs, not small-breed immature dogs, limiting generalizability.

🔍 Key Findings

• No proximal femoral fractures occurred in any of the 184 hips with cerclage wire placement
• Cerclage wire was well tolerated, with no failures or complications related to the wire
• Application of a single cerclage wire took <10 minutes, was cost-effective, and required minimal instrumentation
• 3 postoperative complications (1 fissure, 2 fractures) occurred distal to the cerclage site, near the stem tip, requiring plate/screw fixation
• All dogs returned to normal activity, and all owners were satisfied with the outcome
• Cerclage placement location is critical—must be proximal to the lesser trochanter and close to the calcar to resist hoop strain
• Biomechanical evidence supports that cerclage wires improve resistance to hoop strain and subsidence of cementless stems
• Press-fit cementless stems may settle, but when supported by cerclage, this does not result in fractures even in undersized implants

🔍 Key Findings

• 2.4 mm LCP with a 1.6 mm IM pin had the highest axial stiffness and yield strength among the tested constructs.
• Axial stiffness was significantly higher in the 2.4 mm LCP + 1.6 mm IM pin group compared to 2.7 mm LCP alone (p = .013).
• No significant difference in torsional stiffness was found among groups.
• 2.4 mm LCP + 1.0 mm pin had the lowest stiffness and failure load, underperforming both other constructs.
• All constructs failed via valgus bending, consistent with clinical observations in feline tibial fractures.
• A 1.6 mm pin (~50% canal fill) resulted in superior construct performance vs. 1.0 mm (~30% fill).
• Group 2 (2.4 LCP + 1.6 mm pin) outperformed the 2.7 mm LCP alone in stiffness, despite using a smaller plate.
• Plate–rod constructs may better preserve periosteal blood supply and support minimally invasive stabilization strategies.

🔍 Key Findings

40 dogs underwent splenectomy using 16 bipolar vessel sealing devices (VSDs)
Devices were reused up to 4 times after handwashing and ethylene oxide (EtO) sterilization
Biologic debris was found in 100% of devices, specifically under the transection blade, even after a single use

• Mostly scant (14/16) or mild (2/16) debris

No devices or debris yielded positive aerobic culture after EtO sterilization
EtO sterilization proved microbiologically effective despite visible residue
Perioperative failure rate: 1 device (malfunctioned during first activation)

🔍 Key Findings

• Short working length constructs had significantly higher stiffness and lower strain than long constructs in compression bending (p = 0.0172).
• In tension bending, short constructs also had higher precontact stiffness and lower strain, but this reversed after transcortical contact (~150 N).
• Transcortical contact increased stiffness only in long constructs, producing a bilinear load-displacement curve.
• Postcontact stiffness was higher in long constructs, but this may not reflect clinical benefit due to risks of high interfragmentary strain.
• Short working length reduced strain at multiple ROIs under both loading conditions, including over fracture gap (Tables 1–3).
• Increased working length promoted stress concentration and deformation, especially in compression bending.
• In vitro benefits of long constructs (via contact stability) may not translate to healing, as repetitive loading could increase plate strain and bone resorption.
• Plate strain was effectively mapped using 3D digital image correlation, confirming regional strain differences between configurations.

🔍 Key Findings Summary

• IMN provides relative stability, resists bending/torsion due to central axis alignment
• Larger diameter nails = exponentially greater stiffness (∝ D⁴)
• Trade-off: Larger interlocking holes weaken fatigue strength of the nail
• Reaming increases contact/stability but has pros/cons:
  • Improves outcomes in closed fractures
  • May reduce endosteal blood flow in thin-walled bones (e.g., cats)
• Design advances:
  • Angle-stable IMN reduce rotational slack
  • Expandable nails simplify insertion but may compromise removal or compressive load resistance
  • Precontoured nails match bone curvature but lack consistent clinical superiority
• Material debates continue (e.g., titanium vs. stainless steel vs. magnesium)