Biomechanical Properties of the Cranial Dura Mater with Puncture Defects : An In Vitro Study

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J Korean Neurosurg Soc. 2019;62(4):382-388

Publication date (electronic) : 2019 May 16

doi : https://doi.org/10.3340/jkns.2018.0130

Hasan Emre Aydın¹, Ceren Kızmazoglu^,2, Ismail Kaya¹, Bugra Husemoglu³, Gulden Sozer⁴, Hasan Havıtcıoglu³, Ali Arslantas⁵

¹Department of Neurosurgery, Kutahya Health Science University, Kutahya, Turkey

²Department of Neurosurgery, Dokuz Eylul University School of Medicine, Izmir, Turkey

³Department of Biomechanics, Dokuz Eylul University School of Medicine Health Science Institute, Izmir, Turkey

⁴Department of Pathology, Forensic Medicine Institution , Izmir, Turkey

⁵Department of Neurosurgery, Eskişehir Osmangazi University School of Medicine, Eskisehir, Turkey

Address for reprints : Ceren Kizmazoglu, M.D. Department of Neurosurgery, Dokuz Eylul University School of Medicine, 35340 Balçova, Izmir 35000, Turkey Tel : +90-232-412-33-01, Fax : +90-232-412-97-97, E-mail : ceren.kizmazoglu@gmail.com

Received 2018 June 14; Revised 2018 July 31; Accepted 2018 September 1.

Abstract

INTRODUCTION

The dura mater is a thick fibrous membrane that envelops the arachnoid mater and comprises fibroblasts and extracellular collagen. Although spinal dura mater is primarily arranged in a longitudinal orientation, the cranial dura mater is thicker and possesses isotropic viscoelastic properties [2,14,17,23]. The dura mater is a viscoelastic material that resists high strain and plays a vital role, besides the cerebrospinal fluid, in protecting sensitive areas of the brain and spinal cord from impact [17,25,26]. Although the dura mater protects brain parenchyma, it may be affected by trauma, iatrogenic causes (e.g., surgery and lumbar puncture) and/or tumour invasion. Post-dural puncture headache is an iatrogenic condition attributed to the leakage of cerebrospinal fluid into the epidural space. Reportedly, low cerebrospinal fluid pressure and cerebral vasodilatation are the two major mechanisms underlying this type of headache [1,8,9]. In addition, the estimated incidence of post-dural puncture headache is 1.5–8.1% [4,10,20]. Several clinical studies have reported that needle diameter, needle type and number of failed puncture attempts play a critical role in the development of post-dural puncture headache [10,13,18].

The recent few years have witnessed an upsurge in interest in dura mater biomechanics; however, little research has been conducted to investigate the various biomechanical aspects of lumbar dura mater biomechanics after puncture [7]. Lately, a novel cone-shape microneedle array has been designed and tested in the porcine cranial dura mater for the treatment of hydrocephalus [16]; this implant passes through the dura mater to ensure a channel for the flow of cerebrospinal fluid. Despite our best efforts, nonetheless, we could find no biomechanical study in the literature that reported on the cranial dura mater after puncture(s). Prompted by the lack of studies in this field, the present study aimed to investigate the nature of dura mater biomechanics following the introduction of puncture defect(s).

MATERIALS AND METHODS

Sample preparation

We obtained 28 cranial dura mater specimens during autopsy from the right and left frontal regions of seven participants (three males, four females; mean age, 44.57±11.58 years [range, 31–62]). Of note, all the specimens were fresh and not fixed with formalin. We excised the dura mater widely to prevent mechanical damage. Besides the freeze-thaw effect, refrigerant protection could result in significant variations in the mechanical response of tissues. Thus, in this study, all the specimens were frozen at the same cooling rate and were stored at −20°C; the frozen specimens were thawed at 4°C for 24 hours before performing the tests. Furthermore, the specimens were thawed at room temperature (20–25°C) for 6 hours before mechanical testing.

A customised die was used to cut the samples from the human dura mater and other dura substitutes, followed by random distribution of the specimens into four groups as previously mentioned. We prepared all the samples according to the Japanese Industrial Standard (JISK6251-5 [2004]). This standard dumbbell-shaped model describes the shape of the elastic material to determine the tensile stress-strain properties by Japanese Standards Association. During insertion, a 20 G (0.812 mm)×90 mm Quincke spinal needle (Egemen International Inc., Izmir, Turkey) was used to create puncture defects (Fig. 1) in the tissue specimens. The insertion was automated with constant velocity, in which the bevel tip was parallel to the specimen (Fig. 2). Fig. 3 illustrates the puncture defects, with the dimensions and orientation of the dura mater samples.

Fig. 1.

A : Dimensions of the cranial dura mater specimens showing. B : Dimensions of the 20 G Quincke needle (Egemen International Inc., Izmir, Turkey). SL : shoulder length, GL : gauge length, GW : gauge width, TL : total length.

Fig. 2.

A and B : The bevel tip needle stylet and needle cannula.

Fig. 3.

Puncture defects before the uniaxial tension test. A : One-puncture defect (arrow). B : Two-puncture defects (arrow). C : Three puncture defects (arrow).

Prior to testing, we measured and recorded the thickness of the samples using a digital caliper micrometer gauge (model number SS17DV150, Zhejiang, China). Thickness changes due to specimens. A customised system was fabricated to simulate in vitro conditions. In addition, a customised cup was filled with artificial cerebrospinal f luid (sodium chloride [NaCl], 134 mM; potassium chloride [KCl], 2.5 mM; magnesium chloride [MgCl₂], 1.3 mM; calcium chloride [CaCl₂], 2 mM; dipotassium hydrogen phosphate [K₂HPO₄], 1.25 mM; sodium hydrogen carbonate [NaHCO₃], 26 mM D-glucose) and heated to simulate physiological temperature (37°C).

Mechanical analyses

We used an axial compression device (AG-IS 10 kN; Shimadzu Corporation, Kyoto, Japan) for mechanical analyses. Uniaxial tension was set according to JISK6251-5 standards, and the device was equipped with a 500-N load cell. All the tests were performed at a displacement rate of 10 mm/min at 36.91±0.36°C in a customised container filled with saline solution (Fig. 4). We recorded and assessed the mean maximum tensile strength using TRAPEZIUM X Materials testing software version 1.1.2 (Shimadzu Corporation). Hooke’s law is commonly expressed in terms of normalized parameters by calculating stress. The tensile stress calculation by Hooke’s law is as follows :

Fig. 4.

The test setup (A) and white arrows show (B, left to right) heating element, waterproof sensor, digital thermometer controller.

Hooke’s equation-stressMPa=P/A

where A is the loaded cross-sectional area under tension and P is the loaded force in Newtons.

Young’s modulus, or elastic modulus, is the measure of the elastic deformation of the material under force. Young’s modulus is equal to the longitudinal stress divided by the strain.

RESULTS

Table 1 summarises the mean tensile strength, Young’s modulus and thickness of the specimens used in this study. The mean maximum tensile strengths for groups I, II, III, and IV were 8.35±3.16, 8.22±3.32, 7.13±1.77, and 6.94±1.93 MPa, respectively. Fig. 5 shows the curves resulting from the equations for the stress/strain ratio. In addition, the mean Young’s modulus for groups I, II, III, and IV were 77.86±41.47, 73.34±30.84, 71.59±12.67, and 86.01±20.14 MPa, respectively.

Table 1.

The mean values of thickness, maximum tensile strength and Young’s modulus of human cranial dura mater in all the groups

Fig. 5.

This figure shows the curves resulting from the equations for the stress/strain ratio. Stress-strain curves for all groups (n=28) with a displacement rate of 10 mm/min.

We observed a significant difference in the specimen thickness between groups II and III (p=0.024), but observed no significant difference in tensile strength among all the groups (p>0.05). However, tensile strength in group IV was lower than that in group I, and no significant difference existed between groups I and IV in the displacement of the specimens during tension (p=0.482). Furthermore, we observed no significant difference in Young’s modulus among all groups (p>0.05). Notably, Young’s modulus could not be calculated for one specimen of group II, three specimens of group III and two specimens of group IV.

DISCUSSION

As the human dura mater possesses both viscous and elastic properties, it is recognised as a viscoelastic material, which is an excellent shock absorber. In their study, van Noort et al. [23] evaluated the mean tensile strength of the human cranial dura mater as 4.70 MPa. Likewise, Wolfinbarger et al. [24] reported that the mean tensile strength of the human cranial dura mater was 6.65±0.14 MPa and McGarvey et al. [14] reported that it was 9.41±1.54 MPa. In our study, the mean tensile strength in group I was 8.35±3.16 MPa.

With regard to the mean Young’s modulus of the human cranial dura mater, van Noort et al. [23] reported it to be 21.3–48 MPa, Wolfinbarger et al. [24] reported it to be 69.50±1.28 MPa and McGarvey et al. [14] reported it to be 61.50±9.60 MPa. In our study, the mean Young’s modulus in group I was 77.86±41.47 MPa. Of note, we could not evaluate Young’s modulus in some groups because of low tensile strength.

Zerris et al. [27] reported that the mean tensile strength of Durepair^® (bovine collagen dural graft; Medtronic, Minneapolis, MN, USA) was 22.70±2.83 MPa. Famaey et al. [3] compared the axial tension in stretchable and non-stretchable expanded polytetraf luoroethylene and reported values of 41.48±3.34 MPa and 32.40±3.80 MPa for stretchable and non-stretchable, respectively. These studies explained that artificial dura mater substitutes were more durable than native human cranial dura mater. Our study supports the fact that the tissue biomechanical properties of novel dura mater graft materials differ from those of cranial dura mater. In the future, it is necessary to ensure that biomechanical properties of artificial graft material are similar to those of human dura mater when developing the new dura mater grafts.

Oh et al. [16] designed a novel microneedle array for the treatment of hydrocephalus and placed the implant on porcine dura mater in a way that it created channels for the flow of cerebrospinal fluid. The cone-shaped microneedle diameter was 0.05 mm, which was pushed by a pressure gun to place the needle into the 0.3-mm thick dura mater 16. In our study, we used an automated insertion technique and constant velocity with a 20-G (0.8 mm) Quincke spinal needle to create puncture defects in the human cranial dura mater.

Comparing the Quincke needle bevel insertion parallel and perpendicular to the spinal dura mater, Reina et al. [18] observed no significant difference in the dura-arachnoid lesion created by the puncture. In addition, using the Quincke needle bevel insertion parallel to the spinal dura mater, Flaatten et al. [5] reported a low incidence of post-dural puncture headache. Of note, the parallel insertion did not cut, but separated the fibres, as illustrated by the longitudinal orientation of the spinal dura mater [5]. Mihic [15] reported that the rate of post-dural puncture headache was lower when the bevel of the Quincke needle was inserted parallel to the spinal dura mater. Furthermore, in their investigation of microscopic structure, Reina et al. [18,19] determined no longitudinal orientation of the collagen and elastic fibres. Although human cranial dura mater possesses isotropic mechanical properties, we inserted the bevel of the Quincke needle parallel to the specimens to simulate the impact.

Reportedly, needle and tissue interaction can be affected by the insertion method (manual, automated, velocity, or direction of the bevel), needle type (Quincke, Sprotte, Tuohy conical, etc.) and tissue characteristics [22]. Mahvash and Dupont [12] reported that the puncture force decreased with increasing velocity during needle insertion. In addition, Lewis et al. [7] investigated puncture forces on human dura mater and reported perpendicularly oriented higher puncture forces bevels. Lybecker et al. [11] reported no significant difference between postdural puncture headache and repeated dural puncture in samples of 1021 patients. However, Seeberger et al. [21] revealed that repeated dural punctures increased post-dural puncture headache in 8034 patients. While Kim and Yoon [6] observed no significant difference in the results between 23 G and 25 G Quincke needle on lumbar puncture attempts, they reported an average of 1.4 lumbar puncture attempts for the 23 G and 1.6 for the 25 G Quincke needle; their success rate in the first attempt was 40% for the 25 G Quincke needle.

In this study, we assessed the effects of one or more dural puncture(s) on dura mater biomechanics under uniaxial tension and observed no significant difference in the displacement of specimens during tension among the groups. In addition, single or multiple punctures exerted no adverse effect on cranial dura mater biomechanics under uniaxial tension, suggesting that single or multiple punctures of the dura mater using a 20 G Quincke needle did not affect tensile stress. Furthermore, the tensile stress decreased in groups II, III, and IV compared to group I, but the difference was not statistically significant.

This study has some limitations. First, this study lacks specimens from children and various needle types to create puncture defects. During uniaxial testing, sample standardisation is imperative for soft tissue biomechanics. In addition, Young’s modulus of the specimens could be affected by various factors, and storage conditions and duration are some of the factors that could affect tissue mechanics. In this study, we used frozen and thawed samples of the dura mater but did not investigate the impact of the freeze-thaw cycle on dura mater biomechanics. Finally, we did not assess age-related characteristics of the dura mater in this study. Thus, further extensive studies are warranted to overcome these limitations and validate the findings of this study.

CONCLUSION

This basic laboratory-based in vitro study is the first to illustrate the effects of puncture(s) on human cranial dura mater under stress tension. During surgery, every puncture or suture on the cranial dura mater could affect the mechanical properties of the dura mater, causing surgical failures in extreme cases. Artificial dura mater have been produced to substitute human dura mater. We also suture or make punctures on artificial dura mater during surgery. During artificial dura mater production, it is important that the substitute has properties that are biologically and biomechanically similar to human dura. Thus, we believe that the present biomechanical study may contribute to the future development of artificial dura mater substitutes and medical needles that exert a relatively lower negative impact on dura mater

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