Research Papers

In Vitro Evaluation of the Acetabular Cup Primary Stability by Impact Analysis

[+] Author and Article Information
Adrien Michel, Romain Vayron

Laboratoire Modélisation et de
Simulation Multi-Echelle,
UMR CNRS 8208,
61 Avenue du Général de Gaulle,
Créteil 94010, France

Romain Bosc

Service de Chirurgie Plastique,
Reconstructrice et Esthétique,
Hôpital Henri Mondor AP-HP,
CHU Paris 12,
Université Paris-Est,
51 Avenue du Maréchal de Lattre de Tassigny,
Créteil 94000, France

Guillaume Haiat

Laboratoire Modélisation et de
Simulation Multi-Echelle,
UMR CNRS 8208,
61 Avenue du Général de Gaulle,
Créteil 94010, France
e-mail: guillaume.haiat@univ-paris-est.fr

1Corresponding author.

Manuscript received May 22, 2014; final manuscript received December 22, 2014; published online February 2, 2015. Assoc. Editor: Joel D. Stitzel.

J Biomech Eng 137(3), 031011 (Mar 01, 2015) (6 pages) Paper No: BIO-14-1221; doi: 10.1115/1.4029505 History: Received May 22, 2014; Revised December 22, 2014; Online February 02, 2015

The implant primary stability of the acetabular cup (AC) is an important parameter for the surgical success of press-fit procedures used for the insertion of cementless hip prostheses. In previous studies by our group (Mathieu, V., Michel, A., Lachaniette, C. H. F., Poignard, A., Hernigou, P., Allain, J., and Haiat, G., 2013, “Variation of the Impact Duration During the in vitro Insertion of Acetabular Cup Implants,” Med. Eng. Phys., 35(11), pp. 1558–1563) and (Michel, A., Bosc, R., Mathieu, V., Hernigou, P., and Haiat, G., 2014, “Monitoring the Press-Fit Insertion of an Acetabular Cup by Impact Measurements: Influence of Bone Abrasion,” Proc. Inst. Mech. Eng., Part H, 228(10), pp. 1027–1034), the impact momentum and duration were shown to carry information on the press-fit insertion of the AC within bone tissue. The aim of the present study is to relate the impact momentum recorded during the AC insertion to the AC biomechanical primary stability. The experimental protocol consisted in testing 13 bovine bone samples that underwent successively series of 15 reproducible mass falls impacts (5 kg, 5 cm) followed by tangential stability testing. Each bone sample was tested with different hole sizes in order to obtain different stability configurations. The impact momentum and the tangential primary stability reach a maximum value for an interference fit equal to around 1 mm. Moreover, a correlation between the impact momentum and the stability was obtained with all samples and all configuration (R2 = 0.65). The implant primary stability can be assessed through the measurement of the impact force signal analysis. This study opens new paths for the development of a medical device which could be used as a decision support system to assist the surgeon during the insertion of the AC implant.

Copyright © 2015 by ASME
Topics: Stability , Bone , Signals
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Fig. 1

Image of the AC implant (Ceraver, Roissy, France) used in the experiments. The surface is textured and roughened to allow better osseointegration.

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Fig. 2

Schematic representation of the experimental setup used for impaction of the AC implant

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Fig. 3

Mechanical setup for transverse testing of AC implant stability

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Fig. 4

Schematic description of the experimental protocol

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Fig. 5

Schematic representation of the AC implant insertion conditions with various cavity diameters: ((a): 49 mm, (b) 49+ mm, (c) 50 mm, (d) 50+ mm, (e) d = 51 mm). The arrows in (c) indicate a stressed state of bone tissue.

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Fig. 6

Variations of I as a function of the impact number during the press-fit insertion of a bone sample

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Fig. 7

Five rf signals (corresponding to the time variation of the force f) measured for the last impact obtained during the press fit insertion of the AC implant. The rf signals correspond to insertion impacts in the same bone specimen with a diameter of 49 mm (black solid line), 49+ (black dashed line), 50 mm (gray solid line), 50+ (gray dashed line), and 51 mm (black dashed dotted line).

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Fig. 8

Average and standard deviations of (a) Ilast and (b) tangential stability f as a function of hole diameter for the same sample as in Fig. 7

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Fig. 9

Average and standard deviation of (a) indicator Ilast and (b) tangential stability f as a function of bone hole diameter for all samples pooled (significant differences are identified by an asterisk)

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Fig. 10

Tangential stability f as a function of the indicator Ilast for the same sample as in Fig. 7

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Fig. 11

Tangential stability f versus indicator Ilast for all data pooled from all bone samples




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