# Promising Poly(ε-caprolactone) Composite Reinforced with Weft-Knitted Polyester for Small-Diameter Vascular Graft Application

Authors: Fu-Jun Wang; Abedalwafa Mohammed; Chao-Jing Li; Lu Wang
Journal: Advances in Materials Science and Engineering
 (2014)

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## Abstract

The present study was designed to improve the mechanical performance of a small-diameter vascular prosthesis made from a flexible membrane of poly(ε-caprolactone) (PCL). PCL reinforcement was achieved by embedding a tubular fabric knitted from polyethylene terephthalate (PET) yarns within the freeze-dried composite structure. The knitting density of PET fabric influenced the mechanical properties of the new vascular graft. Results showed that the composite prototype has good mechanical properties, water permeability, elastic recovery, and suture retention strength. Increases in loop density increased compressive strength and suture retention strength and decreased elastic recovery. The new composite prototype vascular graft has promising potential applications in clinics because of its excellent mechanical properties.


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## Body

## 1. Introduction

Atherosclerotic vascular disease is one of the most common causes of death and disability worldwide [1]. Vascular grafts, which are commercially available, are special tubes that serve as artificial replacements for damaged and diseased blood vessels; these grafts are mainly produced from polyester-knitted or woven fabrics [2, 3] or expanded polytetrafluoroethylene (ePTFE) [4–7]. Polyethylene terephthalate (PET) is well recognised in biomedical applications because of its biocompatibility, resilience, flexibility, durability, and resistance to biodegradation and sterilisation. Whilst PET has been successfully used in large-diameter grafts, small-caliber grafts still show unacceptably high percentages of failure. Blood plasma proteins are absorbed by the graft because of surface forces, eventually resulting in inflammation, infection, thrombus formation, and vessel reclosure [8]. These events may cause thrombosis and induce progressive degradation in permeability, especially in terms of vascular permeability, because of the hemodynamic conditions and mechanical inadequacies of the implants. The major cause of the poor performance of such prostheses is lack of compliance [9]. Thus, utilising vascular prostheses from a biocompatible material with the same structural and mechanical properties as the vascular tissue is ideal [10, 11]. Poly(ε-caprolactone) (PCL) is a promising biodegradable polymer with a long degradation time that has been widely used both in vivo and in vitro [12–16]. PCL small-diameter grafts are promising alternatives to ePTFE grafts because the healing characteristics of the former are better than those of the latter [17]; PCL also presents excellent characteristics, such as biodegradability, biocompatibility, flexibility, and ease of manufacture [17, 18]. PCL has been used as a raw material to produce small-diameter blood vessel scaffolds by electrospinning. However, the mechanical properties of this material cannot comply with vascular graft requirements [19, 20]. Textile fabric parameters, such as fabric design and yarn properties, influence the properties of vascular prostheses (porosity, permeability, and mechanical performances) [21, 22]. In this study, tubular PCL reinforced with different PET-knitted fabric structures to form multilayer composites is considered as a novel biomedical material for preparing vascular grafts. The material imitates human blood vessels, which are composed of three layers. PET-knitted fabric was used to increase the mechanical properties of the PCL prototype vascular graft. The influence of fabric density and yarn properties on the mechanical properties of the PCL/PET composite prototype vascular graft was also investigated.


## 2. Materials and Methods

### 2.1. Materials

PET monofilaments and multifilaments (30D) were purchased from Shaoxing Fangxin Chemical Fibre Company (Zhejiang, China) and used for the weft-knitted tubular fabric. The properties of PET monofilaments and multifilaments are shown in Table1. PCL was purchased from Shenzhen Bright China Industrial Co., Ltd. (Shenzhen, China). Acetic acid was purchased from Sinopharm Chemical Reagent Co., Ltd. (Shanghai, China), and used as a solvent.Table 1
Properties of polyester yarns.
Yarn code*
Yarn count (diner)
Tenacity (cN/dtex)
Elongation at break (%)
Density (g/cm3)
Mono
30 D
3.61
±
0.12
16.36
±
2.35
1.39
Multi
30 D/22 f
3.08
±
0.08
94.40
±
16.78
1.39
*Mono: monofilament; Multi: multifilament.


### 2.2. Methods

A PCL tubular freeze-dried graft was fabricated by dissolving PCL in acetic acid to prepare a 15wt.% solution. This solution was coated on the exterior of a 6 mm diameter PTFE rod, which served as the mould controlling the inside diameter of the tubular scaffold. Additional layers of coating were added to control the wall thickness within0.20±0.02 mm. To reinforce the scaffold, PET yarns were knitted into a 6 mm diameter single jersey-knitted structure using a 25-needle circular weft-knitting machine, which was specially designed and built in our laboratory. Three different densities (low, medium, and high) of knitted fabric were produced according to the codes in Table 2.Table 2
Fabric densities of PET weft-knitted tube fabrics.
NO
1
2
3
4
5
6
Sample code
Mono(1)
Mono(2)
Mono(3)
Multi(1)
Multi(2)
Multi(3)
The density
High
Medium
Low
High
Medium
LowThe PCL solution was coated on both sides of the tubular knitted structure prior to mounting on the 6 mm diameter PTFE rod. After coating, the PCL composite scaffolds were cooled and held at –10°C for 12 h. Afterwards, the scaffolds were freeze-dried at  –60°C under less than 10 Pa pressure for 5 h using an FD-1A-50 freeze drying machine. The scaffolds were subsequently immersed in a series of three distilled water baths, with each immersion lasting for 12 h, to remove residual solvents, as shown in Figure1.(a) Schematic representation of new prototype vascular graft. (b) and (c) Optical images of new prototype vascular grafts.
(a)
(b)
(c)


### 2.3. Characterisation Techniques

#### 2.3.1. Yarn Characterisation

Tensile measurements were performed on a YG061 electronic single yarn strength tester with an initial gauge length of 300 mm according to the Chinese standard GB/T 3916-1997.


#### 2.3.2. Optical Microscopic Studies

The knitted structure was assessed using a Stereo Microscope PXS8-T (Nikon Co., Ltd.). Photos were taken by inserting glass (diameter of 6 mm) into the weft-knitted tubular fabric under 2x magnification.


#### 2.3.3. Geometrical Characteristic

Geometrical characteristics were determined according to ISO Standard 7198 : 1998 [23]. Results were averaged from 10 replicates.Weight and Thickness. The weight and the thickness of the tubular fabrics and prototype vascular grafts were measured using electronic measuring devices. Six-centimeter-long samples were prepared and weights (g) per square meter were calculated from the following:
(1)Weightofsample(gm2)=weightofsample(g)πdL,
where d is the diameter of the sample (m) and L is the length of the sample (m).PCL Content. The PCL content of each sample was calculated using the following:
(2)PCLcontent(%)=(weightofthecompositesamples-weightofpurefabric)×(weightofthecompositesamples)-1*100.Porosity Determination. The porosity (P%) of each sample was calculated from (3). The porosities of the PET weft-knitted tubular fabric and pure PCL prototype vascular graft were directly calculated from their densities:
(3)P(%)=[1-(M100hd)]*100,
where M is the mass per unit area of the sample (g/m2), h is the sample thickness (mm), and d is the density of the material (g/cm3).The porosities of the composite prototype vascular grafts were calculated from the density of composite using the following:(4)DC=(CPET*DPET)+(CPCL*DPCL),
where DC is the density of composite prototype vascular grafts (g/cm3), DPET is the density of the PET (g/cm3), DPCL is the density of the PCL (g/cm3), CPET is the content of PET in the composite (%), and CPCL is the content of PCL in the composite (%).


#### 2.3.4. Scanning Electron Microscopy (SEM)

SEM experiments were performed to analyse the surface morphologies and cross sections of the PCL vascular grafts reinforced with weft-knitted tube fabric. A Jeol JSM-5600LV instrument was used. Before examination, samples were gold-sputtered under nitrogen at an excitation voltage of 15 kv.


#### 2.3.5. Tensile Strength

The tensile strength of the samples (along the longitudinal and radial directions) was tested using a YG-B026H universal mechanical tester (Wenzhou Darong Textile Instrument Co., Ltd., China) according to ISO Standard 7198: 1998 [23] under a strain rate of 50 mm/min. Results were averaged from five replicates.


#### 2.3.6. Water Permeability

A water reservoir was connected to a polyethylene tube. The 2.65 cm long graft (surface area of 1 cm2) was connected to two conductors, and the group was connected to the device. The water reservoir was placed in a location elevated by about 165 cm. The pressure transducer was used to verify that the distal end of the graft was constantly exposed to 120 mmHg pressure. The water (mL) permeating through the wall of the grafts (cm2) over time (min) was collected in a graduated cylinder to calculate the water permeability in mL/cm2 min. Water permeability can be expressed using (5) according to ISO Standard 7198: 1998:
(5)W=QA.


#### 2.3.7. Radial Compression

Radial compression was tested using a YG061 radial compressive apparatus (Laizhou Electronic Instrument Co., Ltd., China). The testing method for the elastic recovery was based on the principles found in [24]. The strain rate was 10 mm/min, and the sample pressure was 50% of their diameter. Results were averaged from three replicates. The elastic recovery of each sample was calculated from (6) according to the curve in Figure 2: (6)E%=[(E1+E2)ET]*100.Figure 2
Calculation of the elastic recovery of prototype vascular grafts.


#### 2.3.8. Suture Retention Strength

The suture retention strength was tested using a YG-B026H universal textile strength tester (Wenzhou Darong Textile Instrument Co., Ltd., China) according to ISO Standard 7198: 1998 [24]. The strain rate was 50 mm/min. Samples were tested in four positions and results were averaged from three replicates. The suture retention strength was calculated in terms of N and grams, similar to [25].


## 2.1. Materials

PET monofilaments and multifilaments (30D) were purchased from Shaoxing Fangxin Chemical Fibre Company (Zhejiang, China) and used for the weft-knitted tubular fabric. The properties of PET monofilaments and multifilaments are shown in Table1. PCL was purchased from Shenzhen Bright China Industrial Co., Ltd. (Shenzhen, China). Acetic acid was purchased from Sinopharm Chemical Reagent Co., Ltd. (Shanghai, China), and used as a solvent.Table 1
Properties of polyester yarns.
Yarn code*
Yarn count (diner)
Tenacity (cN/dtex)
Elongation at break (%)
Density (g/cm3)
Mono
30 D
3.61
±
0.12
16.36
±
2.35
1.39
Multi
30 D/22 f
3.08
±
0.08
94.40
±
16.78
1.39
*Mono: monofilament; Multi: multifilament.


## 2.2. Methods

A PCL tubular freeze-dried graft was fabricated by dissolving PCL in acetic acid to prepare a 15wt.% solution. This solution was coated on the exterior of a 6 mm diameter PTFE rod, which served as the mould controlling the inside diameter of the tubular scaffold. Additional layers of coating were added to control the wall thickness within0.20±0.02 mm. To reinforce the scaffold, PET yarns were knitted into a 6 mm diameter single jersey-knitted structure using a 25-needle circular weft-knitting machine, which was specially designed and built in our laboratory. Three different densities (low, medium, and high) of knitted fabric were produced according to the codes in Table 2.Table 2
Fabric densities of PET weft-knitted tube fabrics.
NO
1
2
3
4
5
6
Sample code
Mono(1)
Mono(2)
Mono(3)
Multi(1)
Multi(2)
Multi(3)
The density
High
Medium
Low
High
Medium
LowThe PCL solution was coated on both sides of the tubular knitted structure prior to mounting on the 6 mm diameter PTFE rod. After coating, the PCL composite scaffolds were cooled and held at –10°C for 12 h. Afterwards, the scaffolds were freeze-dried at  –60°C under less than 10 Pa pressure for 5 h using an FD-1A-50 freeze drying machine. The scaffolds were subsequently immersed in a series of three distilled water baths, with each immersion lasting for 12 h, to remove residual solvents, as shown in Figure1.(a) Schematic representation of new prototype vascular graft. (b) and (c) Optical images of new prototype vascular grafts.
(a)
(b)
(c)


## 2.3. Characterisation Techniques

### 2.3.1. Yarn Characterisation

Tensile measurements were performed on a YG061 electronic single yarn strength tester with an initial gauge length of 300 mm according to the Chinese standard GB/T 3916-1997.


### 2.3.2. Optical Microscopic Studies

The knitted structure was assessed using a Stereo Microscope PXS8-T (Nikon Co., Ltd.). Photos were taken by inserting glass (diameter of 6 mm) into the weft-knitted tubular fabric under 2x magnification.


### 2.3.3. Geometrical Characteristic

Geometrical characteristics were determined according to ISO Standard 7198 : 1998 [23]. Results were averaged from 10 replicates.Weight and Thickness. The weight and the thickness of the tubular fabrics and prototype vascular grafts were measured using electronic measuring devices. Six-centimeter-long samples were prepared and weights (g) per square meter were calculated from the following:
(1)Weightofsample(gm2)=weightofsample(g)πdL,
where d is the diameter of the sample (m) and L is the length of the sample (m).PCL Content. The PCL content of each sample was calculated using the following:
(2)PCLcontent(%)=(weightofthecompositesamples-weightofpurefabric)×(weightofthecompositesamples)-1*100.Porosity Determination. The porosity (P%) of each sample was calculated from (3). The porosities of the PET weft-knitted tubular fabric and pure PCL prototype vascular graft were directly calculated from their densities:
(3)P(%)=[1-(M100hd)]*100,
where M is the mass per unit area of the sample (g/m2), h is the sample thickness (mm), and d is the density of the material (g/cm3).The porosities of the composite prototype vascular grafts were calculated from the density of composite using the following:(4)DC=(CPET*DPET)+(CPCL*DPCL),
where DC is the density of composite prototype vascular grafts (g/cm3), DPET is the density of the PET (g/cm3), DPCL is the density of the PCL (g/cm3), CPET is the content of PET in the composite (%), and CPCL is the content of PCL in the composite (%).


### 2.3.4. Scanning Electron Microscopy (SEM)

SEM experiments were performed to analyse the surface morphologies and cross sections of the PCL vascular grafts reinforced with weft-knitted tube fabric. A Jeol JSM-5600LV instrument was used. Before examination, samples were gold-sputtered under nitrogen at an excitation voltage of 15 kv.


### 2.3.5. Tensile Strength

The tensile strength of the samples (along the longitudinal and radial directions) was tested using a YG-B026H universal mechanical tester (Wenzhou Darong Textile Instrument Co., Ltd., China) according to ISO Standard 7198: 1998 [23] under a strain rate of 50 mm/min. Results were averaged from five replicates.


### 2.3.6. Water Permeability

A water reservoir was connected to a polyethylene tube. The 2.65 cm long graft (surface area of 1 cm2) was connected to two conductors, and the group was connected to the device. The water reservoir was placed in a location elevated by about 165 cm. The pressure transducer was used to verify that the distal end of the graft was constantly exposed to 120 mmHg pressure. The water (mL) permeating through the wall of the grafts (cm2) over time (min) was collected in a graduated cylinder to calculate the water permeability in mL/cm2 min. Water permeability can be expressed using (5) according to ISO Standard 7198: 1998:
(5)W=QA.


### 2.3.7. Radial Compression

Radial compression was tested using a YG061 radial compressive apparatus (Laizhou Electronic Instrument Co., Ltd., China). The testing method for the elastic recovery was based on the principles found in [24]. The strain rate was 10 mm/min, and the sample pressure was 50% of their diameter. Results were averaged from three replicates. The elastic recovery of each sample was calculated from (6) according to the curve in Figure 2: (6)E%=[(E1+E2)ET]*100.Figure 2
Calculation of the elastic recovery of prototype vascular grafts.


### 2.3.8. Suture Retention Strength

The suture retention strength was tested using a YG-B026H universal textile strength tester (Wenzhou Darong Textile Instrument Co., Ltd., China) according to ISO Standard 7198: 1998 [24]. The strain rate was 50 mm/min. Samples were tested in four positions and results were averaged from three replicates. The suture retention strength was calculated in terms of N and grams, similar to [25].


## 2.3.1. Yarn Characterisation

Tensile measurements were performed on a YG061 electronic single yarn strength tester with an initial gauge length of 300 mm according to the Chinese standard GB/T 3916-1997.


## 2.3.2. Optical Microscopic Studies

The knitted structure was assessed using a Stereo Microscope PXS8-T (Nikon Co., Ltd.). Photos were taken by inserting glass (diameter of 6 mm) into the weft-knitted tubular fabric under 2x magnification.


## 2.3.3. Geometrical Characteristic

Geometrical characteristics were determined according to ISO Standard 7198 : 1998 [23]. Results were averaged from 10 replicates.Weight and Thickness. The weight and the thickness of the tubular fabrics and prototype vascular grafts were measured using electronic measuring devices. Six-centimeter-long samples were prepared and weights (g) per square meter were calculated from the following:
(1)Weightofsample(gm2)=weightofsample(g)πdL,
where d is the diameter of the sample (m) and L is the length of the sample (m).PCL Content. The PCL content of each sample was calculated using the following:
(2)PCLcontent(%)=(weightofthecompositesamples-weightofpurefabric)×(weightofthecompositesamples)-1*100.Porosity Determination. The porosity (P%) of each sample was calculated from (3). The porosities of the PET weft-knitted tubular fabric and pure PCL prototype vascular graft were directly calculated from their densities:
(3)P(%)=[1-(M100hd)]*100,
where M is the mass per unit area of the sample (g/m2), h is the sample thickness (mm), and d is the density of the material (g/cm3).The porosities of the composite prototype vascular grafts were calculated from the density of composite using the following:(4)DC=(CPET*DPET)+(CPCL*DPCL),
where DC is the density of composite prototype vascular grafts (g/cm3), DPET is the density of the PET (g/cm3), DPCL is the density of the PCL (g/cm3), CPET is the content of PET in the composite (%), and CPCL is the content of PCL in the composite (%).


## 2.3.4. Scanning Electron Microscopy (SEM)

SEM experiments were performed to analyse the surface morphologies and cross sections of the PCL vascular grafts reinforced with weft-knitted tube fabric. A Jeol JSM-5600LV instrument was used. Before examination, samples were gold-sputtered under nitrogen at an excitation voltage of 15 kv.


## 2.3.5. Tensile Strength

The tensile strength of the samples (along the longitudinal and radial directions) was tested using a YG-B026H universal mechanical tester (Wenzhou Darong Textile Instrument Co., Ltd., China) according to ISO Standard 7198: 1998 [23] under a strain rate of 50 mm/min. Results were averaged from five replicates.


## 2.3.6. Water Permeability

A water reservoir was connected to a polyethylene tube. The 2.65 cm long graft (surface area of 1 cm2) was connected to two conductors, and the group was connected to the device. The water reservoir was placed in a location elevated by about 165 cm. The pressure transducer was used to verify that the distal end of the graft was constantly exposed to 120 mmHg pressure. The water (mL) permeating through the wall of the grafts (cm2) over time (min) was collected in a graduated cylinder to calculate the water permeability in mL/cm2 min. Water permeability can be expressed using (5) according to ISO Standard 7198: 1998:
(5)W=QA.


## 2.3.7. Radial Compression

Radial compression was tested using a YG061 radial compressive apparatus (Laizhou Electronic Instrument Co., Ltd., China). The testing method for the elastic recovery was based on the principles found in [24]. The strain rate was 10 mm/min, and the sample pressure was 50% of their diameter. Results were averaged from three replicates. The elastic recovery of each sample was calculated from (6) according to the curve in Figure 2: (6)E%=[(E1+E2)ET]*100.Figure 2
Calculation of the elastic recovery of prototype vascular grafts.


## 2.3.8. Suture Retention Strength

The suture retention strength was tested using a YG-B026H universal textile strength tester (Wenzhou Darong Textile Instrument Co., Ltd., China) according to ISO Standard 7198: 1998 [24]. The strain rate was 50 mm/min. Samples were tested in four positions and results were averaged from three replicates. The suture retention strength was calculated in terms of N and grams, similar to [25].


## 3. Results and Discussion

### 3.1. Yarn Tensile Strength

Figure3 shows the tensile measurement results. The monofilament yarn showed slightly higher tenacity than the multifilament yarn, which is attributed to differences in the fibre composition of each sample. Multifilament yarns are known to be significantly less stiff and show lower compressive strengths than monofilament yarns [26].Figure 3
Elongation-strength curves of polyester yarns.


### 3.2. PET Tubes Fabric

Figure4 shows optical microscopic images of the PET tube fabrics. The images illustrate that loop cohesion and the cover factor are significantly better in the multifilament yarns (Figures 4(d), 4(e), and 4(f)) than in the monofilament yarns (Figures 4(a), 4(b), and 4(c)) because of the higher friction coefficient of the former compared with that of the latter. In addition, the loop density of the weft-knitted tube fabric can be observed: Figures 4(a) and 4(d) show high densities, whilst Figures 4(c) and 4(f) show low densities.Optical microscopic images of the structures of weft-knitted fabric (X2): (a)–(c) monofilament yarns and (d)–(f) multifilament yarns.
(a)
(b)
(c)
(d)
(e)
(f)Table3 shows the loop densities and lengths of the different structures of the weft-knitted tube fabrics. Mono(1) and Multi(1) have higher densities than Mono(3) and Multi(3), respectively.Table 3
Density of PET monofilament and multifilament weft-knitted tube fabrics.
Number
Sample code
Wale/(50 mm)
Course/(50 mm)
Density/fabric (2500 mm2)
Length of loop (mm)
A
Mono(1)
32.0
67.3
2153.0
1.6
B
Mono(2)
29.2
71.4
2086.5
1.8
C
Mono(3)
19.3
72.7
1401.5
2.6
D
Multi(1)
31.1
63.0
1959.0
1.6
E
Multi(2)
25.1
68.6
1723.2
2.1
F
Multi(3)
15.8
69.6
1098.5
2.9


### 3.3. Geometrical Characteristic of Composite Prototype Vascular Grafts

Table4 shows the geometric characteristic of the new composite prototype vascular graft. Fabric density generally affected the geometrical properties of the PCL composite vascular grafts. When the PCL (%) was kept constant, increasing the fabric density increased the weight (g/m2) and thickness (mm) of the resultant fabric. However the porosity of the PCL composite vascular grafts has no correlation effect with fabric densities, due to manual compositing, as seen in Table 4. The new composite prototype vascular graft was thinner and lighter and showed better porosity than commercial ePTFE vascular grafts (Thin Wall). This result indicates that the new composite prototype vascular graft has promising potential in tissue engineering applications.Table 4
Characteristics of new composite prototype and ePTFE commercial vascular grafts.
Samplecode
Fabric density (loop/2500 mm2)
Thickness(mm)
Weight(g/m2)
PCL content(%)
Porosity(%)
Mono(1)
2153.0
0.275
±
0.02
165.8
±
15.02
90.81
±
0.87
48.42
±
4.67
Mono(2)
2086.5
0.260
±
0.01
135.93
±
5.81
90.69
±
0.67
55.49
±
3.46
Mono(3)
1401.5
0.167
±
0.02
126.19
±
15.0
90.14
±
0.72
35.47
±
4.6
Multi(1)
1959.0
0.235
±
0.02
157.1
±
10.01
90.71
±
0.57
43.88
±
3.58
Multi(2)
1723.2
0.193
±
0.02
131.50
±
6.56
90.66
±
0.66
41.54
±
7.27
Multi(3)
1098.5
0.187
±
0.01
115.75
±
9.54
90.03
±
0.81
49.07
±
4.2
ePTFE
—
0.458
338
—
45.63


### 3.4. SEM

Microporous structures of PCL were fabricated using the freeze-drying method. Figure5 shows SEM images of the surface and cross section of PCL reinforced with weft-knitted fabric as well as the surface section of the ePTFE vascular graft. PCL reinforced with weft-knitted fabric showed a pore size range of 10 µm and higher, which indicates that this sample can be used for cell patterning and other clinical applications. The porosity of the new composite prototype was similar to that of ePTFE. Compared with the control ePTFE, however, the porosity of the pure PCL vascular graft yielded decreases in the mechanical properties of the sample.SEM images of microstructures of (a) surface section, (b) cross section of PCL composite prototype vascular graft, and (c) surface section of ePTFE vascular graft.
(a)
(b)
(c)


### 3.5. Tensile Strength of the PCL/PET Composite Prototype Vascular Grafts

Composite vascular grafts with the strength and stability of a knitted structure combine the elasticity and blood-proof properties of PCL. Table5 shows the breaking strength and elongation at break in longitudinal and circumferential direction of the PCL composite vascular grafts with the different fabric density of the PET fabric. Variations in breaking strength and elongation at break are due to variations in fabric weight. The breaking strength in longitudinal direction is slightly lower than the ePTFE graft and the breaking strength in circumferential direction is better than the ePTFE graft. It is indicated that the composite PCL graft is of the potential clinical application for the breaking strength.Table 5
Effect of fabric density on breaking strength and elongation at break.
Sample code
Longitudinal
Circumferential
Elongation at break (%)
Breaking stress (MPa)
Elongation at break (%)
Breaking stress (MPa)
Mono(1)
48.0
±
12.4
12.7
±
0.2
167.8
±
11.5
7.1
±
0.1
Mono(2)
58.9
±
16.8
13.3
±
0.2
160.4
±
15.5
5.4
±
0.3
Mono(3)
42.3
±
3.2
19.2
±
0.1
173.0
±
0.3
9.8
±
0.1
Multi(1)
48.3
±
8.4
16.0
±
0.2
128.5
±
9.0
6.4
±
0.02
Multi(2)
30.2
±
11.6
12.9
±
0.4
141.2
±
5.1
4.8
±
0.3
Multi(3)
43.3
±
11.8
21.3
±
0.2
167.1
±
1.2
9.4
±
0.1
ePTFE
59.6
±
4.4
24.7
±
1.4
—
4.67


### 3.6. Water Permeability

The water permeability of the PCL/PET composite prototype small-diameter vascular graft is zero (Table6). In general, the water permeability of all of the samples was suitable for biomedical applications; according to some references, materials with a water permeability of less than 300 mL/cm2 min may be employed in biomedical uses [23, 27]. Our results are similar to those observed in ePEFE vascular grafts produced by Vascutek. Compared with knitted and woven grafts produced by Sam Company, however, the water permeability of our graft was lower.Table 6
Water performance of PCL/PET composite prototype and commercial ePTFE vascular grafts.
Sample code
All our samples
Woven
Knitted
ePTFE
Manufactures
Our work
Vascutek
Water permeability (mL/cm2/min)
0
75.73
1126.3
0


### 3.7. Radial Compressive Strength of the PCL/PET Composite Prototype Vascular Grafts

General analysis of Figure6 shows that all of the samples have acceptable compressive strengths and elastic recoveries. Figure 6 and Table 7 indicate that fabric density exerts notable influences on the compressive strength and elastic recovery of the resultant graft. Amongst the fabric densities analysed, the vascular grafts produced with fabric densities of 2153.0 and 2086.5 loop/2500 mm2 (monofilament and multifilament, resp.) showed better ability to resist mechanical compression and lower elastic recovery than the vascular grafts produced with fabric densities of 1401.5 and 1098.5 loop/2500 mm2  (monofilament and multifilament, resp.) when the PCL content (%) was held constant. The vascular grafts produced with fabric densities 2153.0 and 2086.5 loop/2500 mm2 (monofilament and multifilament, resp.) showed the highest compressive strengths and are therefore the thickest samples fabricated. The elastic recoveries of these grafts, however, were relatively low because of the high density of the fabrics.Table 7
Compressive strength and elastic recovery of PCL/PET composite prototype vascular grafts.
Sample code
Fabric density (loop/2500 mm2)
Compressive strength(cN)
Elastic recovery(%)
Mono(1)
2153.0
96.01
93.54
Mono(2)
2086.5
94.25
94.16
Mono(3)
1401.5
90.51
98.64
Multi(1)
1959.0
120.9
92.19
Multi(2)
1723.2
114.7
94.87
Multi(3)
1098.5
105.3
95.90Elastic recovery curves of PCL/PET composite prototype vascular grafts: (a) monofilament and (b) multifilament.
(a)
(b)


### 3.8. Effect of Fabric Density on Suture Retention Strength

Figure7 shows that all of the samples have suture retention strengths within the range of 370–420 g, which is acceptable according to [25]. However, these suture strengths are low compared with those of ePTFE from Vascutek (see Table 8), an observation that may be attributed to differences in thickness between samples. To increase the suture retention strength, the thickness of the sample must be increased.Table 8
Suture strengths at break of PCL/PET composite prototype and ePTFE commercial vascular grafts.
Sample code
Mono(1)
Mono(2)
Mono(3)
Multi(1)
Multi(2)
Multi(3)
ePTFE
Suture strength at break (g)
421.4
±
77.3
412.3
±
113.6
385.5
±
130.2
402.1
±
67.4
394.0
±
120.8
371.0
±
120.8
833.9
±
544.1
Suture strength at break (N)
0.413
0.404
0.378
0.394
0.386
0.364
0.818Suture retention strength curves of prototype vascular grafts with different fabric densities: (a) monofilament and (b) multifilament.
(a)
(b)Figure7 illustrates the effect of fabric density on the suture retention strength. The figure clearly shows that when the fabric density increases, the suture retention strength also increases. This result is attributed to the decrease in distance between the yarns, which leads to stronger suture connections.


## 3.1. Yarn Tensile Strength

Figure3 shows the tensile measurement results. The monofilament yarn showed slightly higher tenacity than the multifilament yarn, which is attributed to differences in the fibre composition of each sample. Multifilament yarns are known to be significantly less stiff and show lower compressive strengths than monofilament yarns [26].Figure 3
Elongation-strength curves of polyester yarns.


## 3.2. PET Tubes Fabric

Figure4 shows optical microscopic images of the PET tube fabrics. The images illustrate that loop cohesion and the cover factor are significantly better in the multifilament yarns (Figures 4(d), 4(e), and 4(f)) than in the monofilament yarns (Figures 4(a), 4(b), and 4(c)) because of the higher friction coefficient of the former compared with that of the latter. In addition, the loop density of the weft-knitted tube fabric can be observed: Figures 4(a) and 4(d) show high densities, whilst Figures 4(c) and 4(f) show low densities.Optical microscopic images of the structures of weft-knitted fabric (X2): (a)–(c) monofilament yarns and (d)–(f) multifilament yarns.
(a)
(b)
(c)
(d)
(e)
(f)Table3 shows the loop densities and lengths of the different structures of the weft-knitted tube fabrics. Mono(1) and Multi(1) have higher densities than Mono(3) and Multi(3), respectively.Table 3
Density of PET monofilament and multifilament weft-knitted tube fabrics.
Number
Sample code
Wale/(50 mm)
Course/(50 mm)
Density/fabric (2500 mm2)
Length of loop (mm)
A
Mono(1)
32.0
67.3
2153.0
1.6
B
Mono(2)
29.2
71.4
2086.5
1.8
C
Mono(3)
19.3
72.7
1401.5
2.6
D
Multi(1)
31.1
63.0
1959.0
1.6
E
Multi(2)
25.1
68.6
1723.2
2.1
F
Multi(3)
15.8
69.6
1098.5
2.9


## 3.3. Geometrical Characteristic of Composite Prototype Vascular Grafts

Table4 shows the geometric characteristic of the new composite prototype vascular graft. Fabric density generally affected the geometrical properties of the PCL composite vascular grafts. When the PCL (%) was kept constant, increasing the fabric density increased the weight (g/m2) and thickness (mm) of the resultant fabric. However the porosity of the PCL composite vascular grafts has no correlation effect with fabric densities, due to manual compositing, as seen in Table 4. The new composite prototype vascular graft was thinner and lighter and showed better porosity than commercial ePTFE vascular grafts (Thin Wall). This result indicates that the new composite prototype vascular graft has promising potential in tissue engineering applications.Table 4
Characteristics of new composite prototype and ePTFE commercial vascular grafts.
Samplecode
Fabric density (loop/2500 mm2)
Thickness(mm)
Weight(g/m2)
PCL content(%)
Porosity(%)
Mono(1)
2153.0
0.275
±
0.02
165.8
±
15.02
90.81
±
0.87
48.42
±
4.67
Mono(2)
2086.5
0.260
±
0.01
135.93
±
5.81
90.69
±
0.67
55.49
±
3.46
Mono(3)
1401.5
0.167
±
0.02
126.19
±
15.0
90.14
±
0.72
35.47
±
4.6
Multi(1)
1959.0
0.235
±
0.02
157.1
±
10.01
90.71
±
0.57
43.88
±
3.58
Multi(2)
1723.2
0.193
±
0.02
131.50
±
6.56
90.66
±
0.66
41.54
±
7.27
Multi(3)
1098.5
0.187
±
0.01
115.75
±
9.54
90.03
±
0.81
49.07
±
4.2
ePTFE
—
0.458
338
—
45.63


## 3.4. SEM

Microporous structures of PCL were fabricated using the freeze-drying method. Figure5 shows SEM images of the surface and cross section of PCL reinforced with weft-knitted fabric as well as the surface section of the ePTFE vascular graft. PCL reinforced with weft-knitted fabric showed a pore size range of 10 µm and higher, which indicates that this sample can be used for cell patterning and other clinical applications. The porosity of the new composite prototype was similar to that of ePTFE. Compared with the control ePTFE, however, the porosity of the pure PCL vascular graft yielded decreases in the mechanical properties of the sample.SEM images of microstructures of (a) surface section, (b) cross section of PCL composite prototype vascular graft, and (c) surface section of ePTFE vascular graft.
(a)
(b)
(c)


## 3.5. Tensile Strength of the PCL/PET Composite Prototype Vascular Grafts

Composite vascular grafts with the strength and stability of a knitted structure combine the elasticity and blood-proof properties of PCL. Table5 shows the breaking strength and elongation at break in longitudinal and circumferential direction of the PCL composite vascular grafts with the different fabric density of the PET fabric. Variations in breaking strength and elongation at break are due to variations in fabric weight. The breaking strength in longitudinal direction is slightly lower than the ePTFE graft and the breaking strength in circumferential direction is better than the ePTFE graft. It is indicated that the composite PCL graft is of the potential clinical application for the breaking strength.Table 5
Effect of fabric density on breaking strength and elongation at break.
Sample code
Longitudinal
Circumferential
Elongation at break (%)
Breaking stress (MPa)
Elongation at break (%)
Breaking stress (MPa)
Mono(1)
48.0
±
12.4
12.7
±
0.2
167.8
±
11.5
7.1
±
0.1
Mono(2)
58.9
±
16.8
13.3
±
0.2
160.4
±
15.5
5.4
±
0.3
Mono(3)
42.3
±
3.2
19.2
±
0.1
173.0
±
0.3
9.8
±
0.1
Multi(1)
48.3
±
8.4
16.0
±
0.2
128.5
±
9.0
6.4
±
0.02
Multi(2)
30.2
±
11.6
12.9
±
0.4
141.2
±
5.1
4.8
±
0.3
Multi(3)
43.3
±
11.8
21.3
±
0.2
167.1
±
1.2
9.4
±
0.1
ePTFE
59.6
±
4.4
24.7
±
1.4
—
4.67


## 3.6. Water Permeability

The water permeability of the PCL/PET composite prototype small-diameter vascular graft is zero (Table6). In general, the water permeability of all of the samples was suitable for biomedical applications; according to some references, materials with a water permeability of less than 300 mL/cm2 min may be employed in biomedical uses [23, 27]. Our results are similar to those observed in ePEFE vascular grafts produced by Vascutek. Compared with knitted and woven grafts produced by Sam Company, however, the water permeability of our graft was lower.Table 6
Water performance of PCL/PET composite prototype and commercial ePTFE vascular grafts.
Sample code
All our samples
Woven
Knitted
ePTFE
Manufactures
Our work
Vascutek
Water permeability (mL/cm2/min)
0
75.73
1126.3
0


## 3.7. Radial Compressive Strength of the PCL/PET Composite Prototype Vascular Grafts

General analysis of Figure6 shows that all of the samples have acceptable compressive strengths and elastic recoveries. Figure 6 and Table 7 indicate that fabric density exerts notable influences on the compressive strength and elastic recovery of the resultant graft. Amongst the fabric densities analysed, the vascular grafts produced with fabric densities of 2153.0 and 2086.5 loop/2500 mm2 (monofilament and multifilament, resp.) showed better ability to resist mechanical compression and lower elastic recovery than the vascular grafts produced with fabric densities of 1401.5 and 1098.5 loop/2500 mm2  (monofilament and multifilament, resp.) when the PCL content (%) was held constant. The vascular grafts produced with fabric densities 2153.0 and 2086.5 loop/2500 mm2 (monofilament and multifilament, resp.) showed the highest compressive strengths and are therefore the thickest samples fabricated. The elastic recoveries of these grafts, however, were relatively low because of the high density of the fabrics.Table 7
Compressive strength and elastic recovery of PCL/PET composite prototype vascular grafts.
Sample code
Fabric density (loop/2500 mm2)
Compressive strength(cN)
Elastic recovery(%)
Mono(1)
2153.0
96.01
93.54
Mono(2)
2086.5
94.25
94.16
Mono(3)
1401.5
90.51
98.64
Multi(1)
1959.0
120.9
92.19
Multi(2)
1723.2
114.7
94.87
Multi(3)
1098.5
105.3
95.90Elastic recovery curves of PCL/PET composite prototype vascular grafts: (a) monofilament and (b) multifilament.
(a)
(b)


## 3.8. Effect of Fabric Density on Suture Retention Strength

Figure7 shows that all of the samples have suture retention strengths within the range of 370–420 g, which is acceptable according to [25]. However, these suture strengths are low compared with those of ePTFE from Vascutek (see Table 8), an observation that may be attributed to differences in thickness between samples. To increase the suture retention strength, the thickness of the sample must be increased.Table 8
Suture strengths at break of PCL/PET composite prototype and ePTFE commercial vascular grafts.
Sample code
Mono(1)
Mono(2)
Mono(3)
Multi(1)
Multi(2)
Multi(3)
ePTFE
Suture strength at break (g)
421.4
±
77.3
412.3
±
113.6
385.5
±
130.2
402.1
±
67.4
394.0
±
120.8
371.0
±
120.8
833.9
±
544.1
Suture strength at break (N)
0.413
0.404
0.378
0.394
0.386
0.364
0.818Suture retention strength curves of prototype vascular grafts with different fabric densities: (a) monofilament and (b) multifilament.
(a)
(b)Figure7 illustrates the effect of fabric density on the suture retention strength. The figure clearly shows that when the fabric density increases, the suture retention strength also increases. This result is attributed to the decrease in distance between the yarns, which leads to stronger suture connections.


## 4. Conclusions

In summary, a new composite prototype vascular graft was successfully fabricated. This vascular graft features excellent pore sizes, tensile strength, water permeability, elastic recovery, and suture retention strength. The graft shows promising potential for composite scaffold development in vascular graft applications and tissue engineering.Fabric density showed significant effects on the mechanical properties of the graft. As the loop density was increased, increases in compressive strength and suture retention strength were observed; decreases in elastic recovery, however, were further noted. Meanwhile the mechanical properties are close to or better than the commercial ePTFE graft, which indicated that the composite PCL graft is promising in potential application for small-diameter vascular graft.



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*Source: 273891-2014-07-10.xml*