Background

Cranial cruciate ligament rupture is one of the most important stifle injuries and a common cause of lameness in dogs [1]. CCLR results in joint instability and leads to the development of degenerative joint disease over time [2–5]. Kinetic analysis is commonly employed for objective lameness evaluation in horses and dogs, among other species [6]. Peak vertical force (PVF) and vertical impulse (VI) are the most accurate parameters for lameness diagnosis [7] and can be measured using pressure sensitive walkways [8–10]. PVF and VI are significantly decreased in dogs with CCLR [6, 11–14].

Vertical force redistribution studies in dogs with CCLR report a significant overload of the contralateral limb [9, 10, 15, 16]. Similar to pedobarographic analysis in humans, the isolated analysis of specific areas of the limb during the stance phase of the stride can be performed in dogs using modern kinetic analysis equipment. Data obtained via these methods can be relevant when clinical decisions and patient follow-up are based on improved weight bearing (transfer of load through the paw to the rest of the limb) [17, 18].

Studies on vertical forces in the pads of dogs [17, 18] are scarce and unrelated to orthopedic disease. The aim of this study was to analyze vertical forces in the pads of dogs affected with CCLR. The description of PVF and VI in dogs with CCLR may contribute for a broader understanding of the changes that result in decreased weight bearing in these patients. It may also represent a more comprehensive method for patient follow-up and the critical evaluation of the surgical techniques currently employed to treat the condition.

Methods

This research was approved by the Bioethics Committee of the Faculty of Veterinary Medicine and Animal Science of the University of São Paulo – FMVZ/USP. Ten healthy Pitbulls (control group) and 10 Pitbulls presenting with unilateral CCLR (CCLR group) were used in this study. Previous informed consent was given for the owners. All dogs were submitted to physical and radiographic examination, and the tibial thrust test prior to kinetic analysis. Dogs were aged between 2 and 6 years and weighed between 20 and 36 kg. Exclusion criteria were obesity, cachexia, pregnancy, estrous, history of previous orthopedic surgery, concurrent systemic or orthopedic disease, and medication of any kind over the preceding 4 weeks (minimum washout period of 4 weeks).

Kinetic analysis

Kinetic analysis was performed on a 1.5 × 0.5-m pressure sensitive walkwaya equipped with a series of 3 plates instrumented with a total of 6864 sensors and connected to a dedicated computer.

Five valid trials were evaluated for each dog. Valid trials consisted of controlled velocity and acceleration in a straight line without sidestepping or deviation of the head. Out of a maximum of 20 consecutive passages recorded, 5 valid trials were selected for each dog. The first 4 passages were always excluded to avoid data collection before dogs were familiar with the setup. Only full stride cycles recorded in the middle of the platform were considered. The same operator (A.N.A.S.) was responsible for valid trail selection and analysis. To avoid potential interferences with kinetic analysis trials were always performed in the morning, before physical examination and before daily physical activities were resumed.

Before each session all sensors were calibrated according to a known standard weight. All trials were started 2 meters before the walkway, so that dogs had enough room to complete two full stride cycles before stepping on the platform. Walking velocity varied between 1.3 and 1.6 m/s and acceleration was kept below ± 0.1 m/s2. Velocity was given by the software as stride length divided by the duration of the stride cycle. Acceleration was controlled based on the difference between initial and final velocity divided by time. For increased strictness and to assure constant velocity, only stance phases with a variation of ± 0.01 seconds between consecutive foot strikes were considered for each leg. Dogs were walking fast during data collection in this study. Given gait analysis at the trot was not intended, only duty factors above 50% were considered. Duty factor ranged from 54.1 to 63.4% (mean, 58%).

Peak vertical force (PVF, Newtons) and vertical impulse (VI, N*s) were calculated from the vertical force curve generated automatically by the softwareb. For each foot strike evaluated, measurements of PVF and VI (expressed as percentage of body weight) were obtained from metacarpal/metatarsal pads and digital pads 2, 3, 4 and 5. These areas were manually outlined according to previously reported methods [18].

Statistical analysis

Normal distribution of the data was investigated using the Kolmogorov-Smirnov test. Analysis of variance (ANOVA) and the Tukey test (post hoc) were used to compare the means and to assess the differences between groups and among pads in the same limb within each group. Gait symmetry between the right and left limbs in control dogs and between the healthy and the diseased limb in CCLR dogs was assessed using the paired Student’s t test. The level of significance was set at 5% (p <0.05). Sample power (difference between means based on standard deviation) greater than 80% confirmed the quality of the data.

Results

The CCLR group consisted of 5 intact males and 5 intact females weighing 31.1 ± 3.9 kg and aged 4.2 ± 1.6 years. All dogs in this group had a history of lameness of at least 1 month duration (2.8 ± 1.5 months) but were not showing signs of acute lameness at the time of data collection. All dogs had been treated with non-steroidal anti-inflammatory drugs, but had completed the minimum washout period. The control group consisted of 4 intact males and 6 intact females weighing 28.8 ± 5 kg and aged 4.5 ± 1.2 years. Age and body weight did not differ between groups. Mean PVF and VI values expressed as percentage of body weight and respective standard deviations are summarized in Tables 1, 2 and 3.

Table 1 Peak vertical force (PVF) and vertical impulse (VI) for total of the limbs (mean ± SD)
Full size table
Table 2 Peak vertical force (PVF) for the pads (mean ± SD)
Full size table
Table 3 Vertical impulse (VI)for the pads (mean ± SD)
Full size table

No gait asymmetries were observed in the control group (Table 1). However, important differences were observed in CCLR dogs. PVF and VI were lower in affected limb than in the contralateral limb and in the fore limbs when compared to control (Table 1), indicating that the affected limb, particularly the contralateral limb, is spared at the expense of the remaining limbs in cases of CCLR. Given no gait asymmetries were observed in the control group, the left and right front and hindlimbs were grouped together (i.e. healthy forelimb and hindlimb) and used as a reference for pad evaluation. In the CCLR group, the most prominent decrease in PVF was documented in the metatarsal pad of the affected limb. Mean PVF values in digital pads 3 and 4 were similar to mean values recorded in control dogs (Tables 2 and 3). Vertical force curves of healthy hindlimbs and hindlimbs with CCLR are shown in Figure 1.

Figure 1
figure 1

Vertical force curve in the pads of a dog affected with CCLR. Force curves reflect vertical force analysis of each footpad of a dog affected with CCLR during a valid passage. The same passage was sagitally separated to facilitate visualization and comparison between the affected and the contralateral hindlimb. The typical M-shaped waveform can be seen in the healthy, but not in the affected hindlimb. Peak vertical force is lower in the metatarsal pad of the affected hindlimb.

Full size image

Discussion

Kinetic analysis is more sensitive than subjective evaluation for lameness diagnosis in dogs [19, 20]. Although craniocaudal forces can also be measured using force plates, such forces are less reliable than PVF and VI for lameness diagnosis in dogs due to greater variability [7, 20]. Vertical forces have 90% sensitivity and specificity for lameness detection and can be accurately documented using pressure sensitive walkways [8, 9, 21], as performed in this study.

Despite the wide popularity of kinetic analysis, studies on kinetic analysis in canine pads are scarce [17, 18, 22]. Changes in vertical forces lead to a decrease in PVF and VI in dogs with CCLR [10–16, 23, 24].

The few kinetic studies on load distribution in canine pads published to date report important contribution of the metatarsal pad for total weight bearing in German Shepherds [18], Labradors and Greyhounds [17]. In this study, the lower mean vertical forces documented in CCLR dogs reflected decreased weight bearing on the metatarsal pad in particular. While vertical forces in the affected limb corresponded to approximately 70% of the mean values documented in control dogs, vertical forces on the metatarsal pad were as low as 30% of controls.

The effect of breed on limb [25, 26] and pad [17, 18]kinetic analysis has been reported in dogs. Therefore dogs of the same breed were used in this study. All dogs had a history of lameness of at least 1 month duration. Lameness may be more severe in acute cases or shortly after surgery [27].

As previously reported, the classical M-shape of the vertical force curve reflects the specific dynamics involved in the stance phase of the stride, that begins with braking (footstrike) and ends with propulsion as the dogs lifts the limb off ground (toe off). The first vertical force peak corresponds to the maximum force generated during braking and is followed by a second peak representing the maximum force generated by propulsion. The valley between both peaks represents the movement of the limb from footstrike to toe off (mid-stance) [6, 18]. The characteristic M-shaped pattern may be absent in faster gaits, particularly in the front limbs. A single force peak may then be visualized due to superimposition of the force peaks corresponding to footstrike and toe off respectively [18, 22].

In this study, the M-shaped waveform typically seen during walking was observed in healthy hindlimbs, but not in hindlimbs affected with CCLR (Figure 1). Whenever the M-shaped waveform was observed the first vertical force peak was associated with the metacarpal or the metatarsal pad and the second with the digital pads, particularly the 3rd and 4th hindlimb pads.

Vertical forces are usually distributed among all pads during the stance phase of the stride in dogs. However, our results suggest that the aforementioned areas were possibly responsible for a higher percentage of weight bearing and for the braking and propulsion vertical force peaks. This may be related to CCLR given the braking phase of the stride is one of the most affected by the instability of the joint due to the cranial movement of the tibia [28], as simulated during physical examination using the tibial thrust test [29]. Vertical force magnitude in metatarsal pad may thus constitute an important parameter for post-surgical follow-up of CCLR cases. Vertical force measurements may also indirectly aid in the identification of residual joint instability with potential impact on weight bearing, as shown in ex vivo studies [30].

Weight bearing can also be measured based on craniocaudal force measurements although this method is less accurate due to lower force magnitudes and greater variability. Also, craniocaudal force measurements require the use of a force plate for evaluation of forces generated in three orthogonal planes during movement. Conversely, vertical forces may be measured in any pressure sensitive walkway at a lower cost.

A setup containing a series of instrumented plates capable of sampling a complete stride cycle during the same passage would reduce examination time and the degree of physical exertion required from subjects [9], while permitting consistent data collection [7, 31]. Good quality portable craniocaudal force measurement systems and pressure sensitive walkways are currently available and yield reliable data despite differences in calibration and PVF readings [9].

Conclusions

The results of this study suggest that evaluation of vertical forces in the pads using pressure sensitive walkways may be a promising method for evaluation of dogs with CCLR. The application of this diagnostic tool in other orthopedic diseases that are currently evaluated based on conventional kinetic analysis [32–35] may also contribute for increased understanding of the weight bearing changes observed in affected dogs.

The relevance of kinematic analysis of the tibiotarsal joint in dogs predisposed to CCLR has been reported [36] and important changes in weight bearing have been observed in the distal limb of affected dogs in this study. A comprehensive assessment of locomotion in these patients may be invaluable for critical evaluation of the surgical techniques currently employed to treat the condition.

Endnotes

a7100 QL Virtual Sensor 3 Mat System, Tekscan Inc. South Boston, MA, USA.

bI-scan 5.231, Tekscan Inc., South Boston, MA,USA.