Objective
The aim of this study was to understand the injury mechanisms of pregnant drivers and associated fetal outcomes.
Study Design
Frontal and rear impact tests using a dummy representing the anthropometry of a pregnant woman were conducted.
Results
In frontal impact tests without a seat belt, abdominal pressure peaked at the point where the dummy contacted the steering wheel. Rear impact tests without a seat belt showed that the dummy moved forward because of rebound and contacted the steering wheel, which was avoided when a seat belt was worn.
Conclusion
Wearing a seat belt reduces abdominal pressure or prevents contact with the steering wheel during collisions.
Pregnancy or fetal safety is likely to become an important issue in efforts to reduce traffic accident fatalities. Connolly et al reported that 6–7% of pregnant women undergo some type of traumatic injury during pregnancy and that about two-thirds of such injuries occur during traffic accidents. Klinich et al also reported that about 130,000 women during late-term pregnancy are involved annually in traffic accidents in the United States and that the annual estimate of abortions or stillbirths ranges from 300–3800. The authors previously analyzed the relationship between the severity of injuries sustained by pregnant women and fetal outcomes using data from Japanese automobile insurance claims and associated accidents, as well as from injuries to pregnant women relative to claims for their fetuses. On the basis of these findings, most claims (46%) were submitted by women who were driving automobiles. However, the results of those studies indicated difficulties with predicting adverse fetal outcomes based on injury severity to the mother after a slight (low-velocity frontal or rear) impact, which is the most frequent type of vehicle accident worldwide. Furthermore, injury severity scores did not significantly differ between pregnant occupants with subsequent spontaneous abortion and those whose pregnancies were uneventful, although the scores were significantly higher among pregnant occupants whose fetuses died, including stillbirth and the death of newborn within 1 month of delivery. Therefore, the injury mechanisms to pregnant women and fetuses should be analyzed under the various circumstances experienced by pregnant women during not only high-impact but also low-impact collisions.
Wearing seat belts reduces both the mortality and injury severity of vehicle occupants. According to previous reports, seat belt use during pregnancy improves fetal outcome after motor vehicle accidents. Therefore, seat belt use by drivers and front seat passengers is legally required in many countries. However, some countries exempt pregnant women from mandatory seat belt use. Thus, pregnant occupants of vehicles might not be wearing seat belts at the time of vehicle accidents and subsequently suffer adverse fetal outcomes. Duma et al and Moorcroft et al assessed the amount of stress exerted on the abdomen of pregnant women using finite element (FE) model simulation. They analyzed injury mechanisms under various delta-V (overall accumulative change in velocity) values experienced by pregnant women during collisions and measured strain at the uterus placenta interface (UPI) during impact as a possible predictor of the adverse fetal outcome using the FE uterus model. Their studies used a numeric model, but their assessments included the simplified interior buck model, which does not represent the detailed contour and features of interior components, such as seat shape and stiffness, the steering wheel, instrument panel, or other components that presumably affect the overall kinematics of the occupant. No other studies have comprehensively examined the responses of pregnant drivers during low-speed impact, especially when not wearing a seat belt. Therefore, neither detailed kinematics of pregnant women involved in vehicle collisions nor the biomechanical effects of seat belts on pregnant women under such circumstances are fully understood. The authors, therefore, conducted a series of sled tests to examine the effect of vehicular impact on an anthropomorphic dummy of a pregnant woman. The seated posture of the dummy was based on seat adjustments made by pregnant Japanese volunteers in an actual passenger vehicle. The mechanisms of injury to pregnant drivers and appropriate predictors of adverse fetal outcome are discussed based on the results.
Materials and Methods
Dummy
The dummy used in this study is the most current version of the Maternal Anthropometric Measurement Apparatus, version 2B (MAMA-2B), developed by First Technology Safety Systems (FTSS) and the University of Michigan Transportation Research Institute (UMTRI). This dummy is based on the Hybrid-3 American Female (AF) fifth-percentile dummy, with the pelvis, sternum, and ribcage modified to accommodate a silicone rubber bladder representing the uterus at 30 weeks of gestation. The AF fifth-percentile dummy represents the smallest among the American female population, with a height of 153 cm. The bladder is roughly spherical, approximately 200 mm in diameter, and contains 3000 mL of water representing the amniotic fluid when in use, but a fetus is not modeled inside. Two pressure sensors are installed on the anterior and posterior surfaces inside the bladder. Other sensor implementation is essentially identical to the conventional Hybrid-3 AF fifth-percentile dummy.
Test setup
The authors previously measured the seated posture of healthy female volunteer drivers at approximately 30 weeks of gestation, in a typical sedan-type passenger vehicle (all results are shown as means ± standard deviation [SD] unless otherwise stated). To represent the status of real-world impact to a passenger vehicle driven by a pregnant woman, the seating position of the dummy was determined from the means of anthropometric values obtained from 7 pregnant women aged 28.7 ± 2.4 years with similar dimensions to the dummy: height, 152.6 ± 3.0 cm; weight, 54.7 ± 2.8 kg; gestation, 30.8 ± 1.0 weeks; abdominal circumference, 86.4 ± 4.2 cm. The authors determined the posture of the dummy at a seat slide position of 70 mm from the full-forward position (50 mm forward from the neutral position) and reclined at 8° (torso angle, 21°), which was the closest position to the mean measurement. The seat, seat belt, and steering wheel installed in the sled buck (full-size model of the interior of a vehicle used for impact testing) were identical to those in the vehicle and placed in the same relative positions.
Test conditions
Two frontal (tests 1 and 2) and 2 rear (tests 3 and 4) impact tests were performed. To represent real-world impact to a passenger vehicle as closely as possible, waveforms measured during flat barrier tests with a delta-V of 13 km/h were applied during the frontal impact tests. A trapezoid waveform sled pulse was applied to the sled with a delta-V of 24 km/h (mean acceleration of 6.5 × g), as defined by Folksam’s test protocol for rear impact tests. Folksam’s test protocol was determined from representative third-party car assessments for rear impacts and was recently incorporated into the European New Car Assessment Program (Euro NCAP). The protocol includes the application of a predetermined acceleration pulse to a sled buck with an actual car seat and then injury to a seated dummy is scored.
Tests were run with (tests 1 and 3) and without (tests 2 and 4) a seat belt. The airbag and seat belt pretensioner were not activated throughout the tests. The overall kinematics of the dummy, such as trajectory during impact, was examined using high-speed video imaging. Quantitative dummy responses, such as the time history of acceleration and pressure on the abdominal bladder of the dummy (hereafter referred to as abdominal pressure) during impact, were also measured and analyzed. The Table shows a matrix summarizing the test conditions.
Test number | Direction of impact | Delta-V (km/h) | Seat belt use |
---|---|---|---|
Test 1 | Frontal | 13 | Belted |
Test 2 | Frontal | 13 | Unbelted |
Test 3 | Rear | 24 | Belted |
Test 4 | Rear | 24 | Unbelted |
Results
Figures 1–4 show the kinematics of the dummy at 50-ms intervals (from 0–150 milliseconds for frontal, from 50–250 milliseconds for rear impact tests) from the initiation of impact taken by a high-speed video camera from the right side of the sled. Figures 5–8 show changes in anterior and posterior abdominal pressure over time during the tests. The abdomen of the dummy slightly contacted the lower rim of the steering wheel at about 70 milliseconds from the initiation of impact in test 1 (belted frontal impact). In test 2 (unbelted frontal impact), the abdomen similarly contacted the steering wheel, whereas the chest did not. The face of the dummy contacted the upper rim of the steering wheel at 130 milliseconds. In test 3 (belted rear impact), the dummy moved 150 mm backward from its initial position and then moved forward because of rebound. The dummy also moved downward at its most forward position, resulting in no contact with the steering wheel. In test 4 (unbelted rear impact), the abdomen of the dummy contacted the steering wheel at 230 milliseconds because of rebound.