Drug Loading on Microneedles

Meng-Hsuan Hsiao, Hsiu-Feng Ye, Ta-Jo Liu, Jane Wang^*

Department of Chemical Engineering, National Tsing Hua University, Hsinchu.

DOI: 10.4236/aces.2019.92016                

Abstract

An experimental study was carried out to investigate the amount of drugs loaded on microneedles. The microneedles were made with poly (lactic acid). Aqueous poly (vinyl alcohol) solutions were prepared as drug solutions. Two drug loading approaches, i.e., dropping and dipping, were examined. It was found that capillary number is the only relevant dimensionless group for the two methods. For the dropping approach, dried drugs will spread near the bottom of a microneedle patch provided the surface tension is low. As for the dipping approach, both a single microneedle and an array of nine microneedles were examined. For a single microneedle, high capillary rises before pulling and pulling speed are two key factors to increase the drug loading volume. For an array of microneedles, the effect of capillary rise owing to the interaction between microneedles would increase the drug loading volume several times higher than a single microneedle of the same dimension.

Keywords

Microneedle, Drug Loading, Dropping, Dipping, Capillary Number, Capillary Rise

1. Introduction

Microneedles (MNs) were first developed by Henry et al. [1] as a new and effective drug delivery system to transport drugs into human bodies in a painless way, since MNs can penetrate human skin but are short enough not to affect the nerve system. Up until now, there are approximately four hundred technical articles studying the different aspects on how to deliver drugs effectively by microneedles [2] .

The definition of a microneedle is not very strict; most MNs are in the solid form with hundreds of needles on a small patch of sizes in the neighborhood of 1 to 4 cm², but a single needle with a diameter much smaller than the conventional injection tip can be called a microneedle [2] .

As of now, there are four types of microneedles, i.e., solid, coated, dissolvable and hollow microneedles [3] [4] , and each type has its advantages and drawbacks. The existing works have been focusing heavily on the materials that can be used to make MNs [4] , the shapes and geometries of MNs for better insertion into human bodies [5] [6] [7] [8] , but most importantly the selection of a suitable drug that can be combined with MNs to effectively deliver drugs into human body. Currently, vaccines such as enterovirus 71 [9] , influenza [10] [11] , hepatitis B [12] , bacillus Calmette-Guérin (BCG) [13] , human immunodeficiency virus (HIV) [14] , human papillomavirus (HPV) [15] , recombinant adenovirus (rADV) [16] , diphtheria [17] , and drugs such as insulin [18] [19] , human growth hormone (hGH) [20] , lidocaine [21] have been considered as drugs suitable for the combination with MNs, just to name a few here. Interested readers may refer to several review articles for more details [2] [3] [22] .

There are multiple ways to deliver drugs into human body through MNs; drugs can be mixed with FDA approved materials, such as biodegradable polymers, including chitosan [23] , poly (vinylpyrrolidone) (PVP) [24] [25] , carboxymethyl cellulose (CMC) [19] , poly(vinyl)alcohol (PVA) [24] [26] , and then molded and dried to make MNs [27] [28] , or drugs can be maintained in liquid form and encapsulated in a hollow space of the MN [29] [30] or injected into an array of hollow MNs [31] . Another approach is to make MNs first, then through different methods, such as ink jet printing [32] [33] [34] , spray coating [16] [35] or dip coating [21] [36] [37] to load drugs on the surface of MNs.

To develop MNs as a useful means for drug delivery, MNs have to be strong enough to penetrate human skin, and the solubility of MNs must be well understood and controlled to make sure that drugs can be diffused into blood vessels and function as expected. Most importantly, the amount of drugs entering human body has to be accurately evaluated for curing or controlling illness effectively. It is easier to control the amount of drugs by mixing the drugs with the materials that are used to make MNs, particularly if MNs are made in two steps and drugs can be distributed on the tip region of MNs [23] [38] .

Since most drugs and vaccines cannot resist high temperature, once they are mixed with the materials to make MNs, the drying process cannot be carried out at high temperature. Freeze drying or drying below 20˚C is common, but may take several days to obtain dried MNs. One simple way that can be applied to reduce the drying time is MNs that do not contain any drugs or vaccines are made first with materials such as PLA [39] [40] and PLGA [40] [41] , since the chosen materials to make MNs are mostly polymers and other additives such as starch [28] [42] , trehalose [20] , β-cyclodextrin [43] [44] and sodium alginate [45] [46] that can resist high temperature, the drying of MNs can be much faster. After MNs are made, solutions that contain drugs or vaccines can be added onto the surfaces of the MN and then dried. The drying time can be substantially reduced because the drug solutions are on the surface of the MNs instead of the inside of the MNs. Dip coating, inkjet printing and spray coating were proposed for this purpose [47] . However, one uncertainty of this approach is the difficulties in estimating the precise drug loading quantity and the topology of the drugs loaded on the surface of MNs after drying.

The present study aims to examine two different but simple approaches to load drug solutions on the surface of MNs. The first approach is dropping; which implies that drops of drug solutions are deposited on the top of a microneedle patch (MNP). The drug solution will cover the entire MNP, then followed by a drying process. Another approach is dipping; where MNs are dipped into a drug solution pool for a moment, then the MNs with drug solution on the surface will be lifted and dried. Gill and Prausnitz examined the dip coating process and found that the amount of loaded drug was influenced by solution viscosity, surface tension and wettability [36] , which are identical as the study on dip coating operation from the fluid mechanical point [48] . Authors from 3M also had previously shown a number of photos on drugs loaded on MNs with repeated dip coating operations [21] . In the recent few years, more and more works involve the application of MNs toward the delivery of various drugs became available, but the fabrication methods vary drastically [49] [50] [51] . The objective of the present study is to analyze the general effect of critical drug solution characters to enable precise control over the drug loading quantity, as well as the topology of the dried drugs loaded on the surface of MNs.

2. Experimental Work

Several MNs made by poly(lactic acid) (PLA) (L-lactide: D, L-lactide = 70:30, inherent viscosity 0.56 dL/g), purchased from Green Square Materials Inc. (Taiwan) were used for the drug loading experiment. A metal mold made by Win Coat Co. (Taiwan) was used to produce several polydimethylsiloxane (PDMS; Sylgard 184) molds, which have low surface energy and it is much easier to remove MNs from the PDMS molds. Three different types of PDMS molds were made to conduct the dropping and dipping experiments separately. For dropping, the size of the PDMS mold is 0.035 × 0.035 m with 578 (17 × 34) conical needles on the mold. The height of each needle is 6 × 10⁻⁴ m, the base diameter is 3 × 10⁻⁴ m, and the distance between two tips of the adjacent needles is 6 × 10⁻⁴ m. As for dipping, both a single conical needle mold and a 0.04 × 0.04 m mold with an array of 1 × 9 conical needles were made. The needle height is 1.2 × 10⁻³ m, the needle base diameter is 600 µm and the distance between two needle tips is 9 × 10⁻⁴ m. It is noted that the needles for the dipping experiment are larger than those for dropping because a flow visualization technique was applied to record the dipping process, and it is easier to observe the fluid motion with larger needles.

A certain amount of PLA was dissolved in acetone to make a 20 wt% PLA solution and was injected on the surface of a PDMS mold. The PDMS mold filled with PLA solution was placed in a vacuum oven operating at 6.67 × 10⁻³ Pa for a few minutes and then was refilled with at least 2 ml of PLA solution. The filled PDMS mold was heated at 150˚C and under 6.67 Pa for 5 hours, and then the MNs were dried and removed from the PDMS mold. As soon as the fabrication process was completed, the digital camera and scanning electron microscope (SEM) images of the needles were taken to evaluate the needle quality. Needle fracture force tests were also applied to make sure the needles could reach the designated strength.

Aqueous PVA solutions were made as the testing solution to study the amount of drugs loaded on the surface of MNs. PVA (MW = 20 - 30 kDa, hydrolysis = 98% - 99%, Chang Chun Co., Taiwan) were dissolved in DI water to make solutions of different viscosities. A fluorocarbon surfactant (Zonyl® FSO, DuPont) was added to the PVA solutions to adjust the surface tension. In order to evaluate the drug loaded on the needle surface, a small amount of fluorescent tracer dye rhodamine 6G (R4127, Sigma) was added into the solutions. Viscosities of PVA solutions were measured by a viscometer (MCR302, Anton Paar, Graz, Austria) at room temperature and surface tensions of the PVA solution were determined by a surface tensiometer (CBVP-A3, Kyowa Interface Science, Japan). The contact angles of PVA solutions on the PLA surface were analyzed by a contact angle meter (FTA 1000B, First Ten Angstroms, USA).

For the dropping experiment, a MNP of size 0.025 × 0.025 m was set up and a certain amount of PVA solution was dropped onto this MNP. If the viscosity of the PVA solution was too high, the liquid drop would take a very long time to level off. We adopted an easy approach by flooding the MNP with 1.5 ml PVA solutions, such that the liquid level was slightly above the needle tips. A visualization technique was applied to record the side view of the slow drying process of the PVA solutions dropped onto the MNP.

As for dipping, it is necessary to control the penetration and lifting speeds so as to evaluate the amount of PVA solution being carried away from the pool and coated on the surface of MNs. A dip coating device was built as shown in Figure 1; a flow visualization device was attached to record the dip coating process for quantitative analysis later. Dipping on a single conical needle was studied first. Then an array of 1 × 9 conical needles was examined later. The amount of a dried drug loaded on MNs was difficult to determine due to its small size. To evaluate the amount of drugs loaded on the needle surfaces accurately, a calibration curve of fluorescent emission intensity vs. rhodamine 6G concentration was developed first. After a needle was lifted up, it was soaked immediately into a reservoir filled with 3 ml DI water for 20 minutes until the model drug was fully dissolved in the water. Finally, the fluorescent emission intensity of the solution was calculated from the calibration curve, then the amount of drugs loaded on the needle surface could be calculated.

3. Results and Discussions

We shall explain the findings on dropping and dipping separately; dropping will be discussed first.

Figure 1. The dip coating apparatus. (A) Optical linear scale. (B) Lighting source. (C) Microneedle loading platform. (D) Fluid reservoir. (E) Fluid visualization system. (F) Motor.

Dropping implies that the liquid drops of a drug solution are deposited on a MNP and the drug solution will spread and cover the whole surface of a MNP before drying commences. However, it may not be easy for drug solutions, especially viscous ones, to spread in a short period of time evenly on a flat surface.

Huppert [52] found that the spreading time t of an axisymmetric viscous liquid drop can be presented in the following equation:

${\left(\frac{3\nu }{gS}\right)}^{1/8}K\left(t\right)=0.894{\left(t\right)}^{1/8}$ (1)

here $\nu \equiv \frac{\mu }{\rho }$ is the kinematic viscosity, g is the gravitational force, S represents

the axisymmetric drop volume and $K\left(t\right)$ is the radius of the drop. Equation (1) only covers the viscous and gravitational effects. If a liquid drop was at the size of ${10}^{-7}$ m³, viscosity of $1.5\times {10}^{-1}$ Pa・s and density of 1050 kg/m³, it may take around 1000 seconds to spread on a flat surface with the size similar to the MNP in the present experiment. For a surface with many needles, it is much harder to predict the liquid spreading time owing to the complexities of MN surface topology and combined viscous and capillary effects. Therefore, we adopted a strategy that is to supply an excessive amount of drug solution to cover the whole MNP and the liquid level is slightly higher than that of needles, then start recording how the drug solution is dried under room temperature (25˚C) to find the final topology of the dried drug on the surface on a MNP. The total amount of drug loaded on a MNP can be estimated with the available solid content of the drug solution deposited on the MNP.

The photos of the MNs used in the dropping test are shown in Figure 2. Variations of the diameters and heights of each microneedle are around $\pm {10}^{-5}$ m. The tipdiameter of each microneedle is around $1.5\times {10}^{-5}~2.5\times {10}^{-5}$ m.

Prausnitz found that surface tension and viscosity are two of the most critical parameters on drug loading, [36] here we also examined the effects of the two parameters. The physical properties of the testing solutions for the dropping test are listed in Table 1. The viscosity and surface tension were varied and the effects of the two parameters were examined. Densities of these solutions are around 1030 to 1060 kg/m³. Note that rhodamine 6G was added to each of the drug solution for flow visualization and the concentration is 2000 µL/mg. The important effects of surface tension and viscosity imply that capillary number Ca is the only critical dimensionless group in this study. Ca is defined as follows:

$\text{Ca}\equiv \frac{\mu V}{\sigma }$ (2)

here $\mu$ is the fluid viscosity, $\sigma$ is the surface tension and V is the characteristic velocity. The characteristic velocity V can be estimated as

$V\equiv \frac{dH}{dt}$ (3)

here H is the distance between the needle tip and the lowest central point of the meniscus after the loaded drug solution is completely dried. For example, if the fluid viscosity is ${10}^{-2}$ Pa・s, surface tension is $4.15\times {10}^{-2}$ N/m, it takes nearly 6 hours to dry the liquid, and is around $4.6\times {10}^{-4}$ m after drying. Since it takes hours to dry the drug solution at room temperature, V defined in Equation (3) is in the neighborhood of O (10⁻⁶), which implies that Ca is very small and the surface tension should be the dominant factor.

Figure 2. Scanning electronic imagines of PLA microneedles. (a) Side view. (b) Top view.

Table 1. Physical properties of test solutions for the dropping experiment.

There are five sets of recorded data with photos showing the variations of the topology of the drug solution surface during the drying process. The photos of the dried drug surfaces are shown in Figure 3. The key points for observation are the point P_f that the dry drug material pinned to the needle surface, and the depth of the dried drug surface represented by H. Data of P_f and H are also given in Figure 3.

We observed that when the drying started, the level of the drug solutions would be lowered gradually owing to solvent evaporation, and the tips of the microneedles would emerge and a meniscus would form between needles when viewing from the front side. The three-phase contact point between the drug solution and the needle surface was also lowered gradually as drying proceeded until a certain point P_f was reached, then the liquid meniscus would be pinned at two ends on the needle surface, but the central part would be more and more curved until drying was complete. The pinned point P_f represents the highest point that the drug is attached to the microneedle, the position of P_f together with the depth H of the drug meniscus would affect the rate and the amount of the drug diffusing into human bodies.

Several comments can be made after examining the results in Figure 3. Comparing between the photos of Cases (A) with Case (B), it is evident that for a more viscous drug solution, P_f appears to be higher, owing to the fact that solvent evaporation will increase the fluid viscosity and a more viscous liquid tends to move slower and dry faster. Note that the solid contents of Case (A) and (B) are different and the total amount of dried drugs in the MNP are also different. Once a surfactant was added and the surface tension of the drug solution was reduced, the results shown in Cases (C), (D) and (E) indicate that P_f would move down and the effects of viscosity appear to be less important. Values of are similar for these three cases, which also verifies the assumption that Ca is small and the effect of surface tension is more critical.

It is difficult for us to determine the 3D topology of the loaded drug accurately on the MNP. As mentioned before, dropping is a simple way to load drugs, but the amount that can be delivered into human body is difficult to be estimated since most of the dried drugs stay near the bottoms of the MNs, which may not be favorable for drug delivery. More detailed pharmacokinetics (PK) analysis may be necessary to detect the amount diffusing into human body for a particular drug. This is beyond the scope of the present study. The important findings here are the effects of viscosity and surface tension on the topology of the loaded drug.

As for the dip coating experiment, several test solutions were prepared. The physical properties of these solutions are given in Table 2. Three pulling speeds, i.e., $V={10}^{-4},{10}^{-3},\text{and}{10}^{-2}$ m/s were set up for the experiments. The concentration of the trace rhodamine 6G was kept the same as the previous dropping experiment.

The experiment on a single microneedle was performed first. Initially the microneedle was lowered just to touch the surface of the drug solution, then the dip coating experiment commenced by penetrating the microneedle into the solution pool at the speed of ${10}^{-5}$ m/s. The penetration depth was set up to be $4\times {10}^{-6}$ m, which is around $1/3$ of the total needle height. The microneedle was then pulled up with three different speeds as specified above. The drug solution was attached to the microneedle and a liquid bridge was formed, then the bridge would break up when as the needled was pulled up and the drug solution would form a donut ring around the microneedle surface. The volume of the ring will determine how much of the drugs will adhere to the microneedle surface. The position and the shape of the ring after drying will influence the amount of drugs and amount of time it takes the drugs to be dissolved in human bodies within a specified period of time.

Figure 3. Photos of dried drug surfaces for the dropping experiment. Red circles are the highest attached points Pf.

Table 2. Physical properties of test solutions for the dipping experiment.

Comparison between two single microneedles under the same dipping and drying condition is the displayed in Figure 4; the difference is that the viscosity of one solution is $\mu =0.1$ Pa・s and another is $\mu =1$ Pa・s. The photos in Figure 4(a) and Figure 4(b) indicate that the capillary rise for the dilute solution was higher. The photos of the rings formed after the liquid bridges were broken on the two microneedle surface are shown in Figure 4(c) and Figure 4(d). It is noted that more drug solution was attached to the microneedle surface for the case with a lower viscosity, and the upper wetting line position was also higher. The initial height of capillary rise might have contributed to the volume attached to the microneedle surface. The shapes of the dried rings on the microneedles are displayed in Figure 4(e) and Figure 4(f); the volumes of the rings shrunk owing to solvent evaporation, gravitational force also pulls the liquid down. However, it is interesting to note that the top and bottom wetting line positions that define the rings improves drastically through the drying process.

There are six sets of test solutions labeled as Cases A-1, A-2, B-1, B-2, C-1 and C-2 in Table 2. The effects of the three critical parameters, i.e., surface tension, viscosity and pulling speed on the wet drug loading volume (DLV) are displayed in Figure 5. It is noted that at the lowest pulling speed $V={10}^{-4}$ m/s, there is not much difference for the six cases as shown at the front row of the data in Figure 5. However, as the pulling speed increases, the drug loading amount increases accordingly, the case with the lower surface tension and lower viscosity has a larger drug loading amount. The effect is more significant as the data at the rear row in Figure 5 indicated. It is obvious that as the pulling speed increases, decreasing both surface tension and viscosity can increase the drug loading volume.

Figure 4. The shapes of the attached drug solution ring before and after drying of a single microneedle. Photos (a) and (b): dip into 400 μm depth. Photos (c) and (d): after pulling out. Photos (e) and (f): complete drying.

Figure 5. Drug loading volume (DLV) as functions of surface tension, pulling velocity and fluid viscosity.

It is necessary to analyze the effects of other factors, such as inertial or gravitational force on the drug loading amount. The analysis can be focused on three dimensionless groups, i.e., Reynolds number Re, Stokes number St and capillary number Ca. Re and St are defined as follows:

$\mathrm{Re}\equiv \frac{\rho V\mathcal{l}}{\mu }$ (4)

$St\equiv \frac{\rho g{\mathcal{l}}^2}{\mu V}$ (5)

The characteristic length $\mathcal{l}$ has to be defined first. In the present study, $\mathcal{l}$ is defined as:

$\mathcal{l}\equiv \frac{\Psi }{\xi }$ (6)

here, $\Psi$ is the total drug solution attached to the microneedle surface, and $\xi$ is the wetted surface. For example, if the fluid viscosity is 1 Pa s, surface tension is $1.8\times {10}^{-2}$ N/m and the pulling speed is ${10}^{-2}$ m/s, we found that the liquid drug volume $\Psi$ on the microneedle surface was around $1.95\times {10}^{-11}$ m³, while the wetted surface $\xi$ of the ring bounded by two wetting lines was around $5.08\times {10}^{-7}$ m², thus $\mathcal{l}\equiv 3.84\times {10}^{-5}$ m.

Values of these dimensionless groups for one representative case are given in Table 3. It is noted that the values of St and Re are relatively small when compared with that of Ca. Therefore, the effect of gravitational and inertial forces are less relevant in this analysis, Ca is the only meaningful dimensionless group. The data in Figure 5 can be plotted with DLV vs. Ca, which are shown in Figure 6. Generally speaking, DLV goes up as Ca increases, however, there are three data points A, B and C that are somewhat out of the track. A least-square fitting of the data points excluding these three data points lead to

$DLV=\alpha {\text{Ca}}^{\beta }$ (7)

with $R^2=0.944$ , $\alpha =2\times {10}^{-4}\text{and}\beta =0.118$ . Note that for dip coating with $\text{Ca}\ll 1$ , the analytical solution of film thickness for flat substrate is [48]

$h\propto {\text{Ca}}^{\frac{1}{6}}$ (8)

Table 3. Values of the three dimensionless groups in the dipping experiment.

Figure 6. Correlation between DLV and Ca for the dipping experiment. Excluding Points A, B, and C, the correlation coefficient (R2) is 0.9044 with equation y = 0.0002 × 0.118.

Therefore, the dependence of DLV on Ca is somewhat close to the conventional dip coating operation for flat films. As for the three data points A, B and C, it is noted that the three cases correspond to low surface tension ( $\sigma =1.8\times {10}^{-2}$ N/m), higher pulling speed and lower viscosity. Point B has the highest pulling speed ( $V={10}^{-2}$ m/s) and lowest viscosity ( $\mu ={10}^{-1}$ Pa・s), and DLV is the highest among all data points.

It is noted that the presented dip coating is not a steady-state operation, once the needle penetrates into the drug solution pool, the capillary rise appears immediately. After the operation switches from penetration to pulling up, the amount of drug solution attached on the microneedle surface can be quite different for each case. In addition to surface tension and viscosity that would influence the capillary rise, the effect of wetting angle can also be critical. The data of wetting angle $\theta$ in Table 2 indicate that if the surface tension is maintained at $4.15\times {10}^{-2}$ N/m, varying the fluid viscosity only influences the wetting angle slightly, once the surface tension is lowered to $1.8\times {10}^{-2}$ N/m, the wetting angle drops sharply and for the case with the lowest fluid viscosity, and wetting angles $\theta$ is the smallest. The wetting angle $\theta$ will also influence the liquid climbing, or capillary rise of the drug solution. Figure 7 displays the photos of capillary rise for several cases before pulling up. Apparently for the cases with high surface tension $\sigma =4.15\times {10}^{-2}$ N/m, the capillary rise is not significant. However, the three cases with lower surface tension $\sigma =1.8\times {10}^{-2}$ N/m clearly demonstrate that significant capillary rise would appear. Lower fluid viscosity would increase the capillary rise, but the effect is less significant than that of surface tension. It is concluded that lowering the surface tension, fluid viscosity and wetting angle can increase the capillary rise, which will lead to an increase of the drug loading amount, and surface tension is clearly the dominant factor. The pulling speed is also an important factor. Increasing the pulling speed with the case of high capillary rise would increase DLV substantially.

As for an array of microneedles, the speed and height of capillary rise are much more significant than those of a single needle. For a dilute solution of viscosity $\mu ={10}^{-1}$ Pa・s, the drug solution will climb up to the roots of the microneedles instantly. Figure 8 demonstrates how fast the drug solution can climb up to one-half of the microneedle height. As the fluid viscosity increases, the time for the drug solution to reach the roots will also be increased. For the case with $\mu ={10}^{-1}$ Pa・s, it took 1 minute to reach one-half of the microneedle height, while for a solution with $\mu =1$ Pa・s, the time to reach one-half of the microneedle height is around 2.5 minutes. It is also noted that the front of the capillary rise is not flat. The central part of the drug solution climbs faster than the two sides.

A comparison of capillary rise between a single microneedle and an array of microneedles is shown in Figure 9. The initial conditions are the same, after penetrating 30 $\text{μm}$ deep into the drug solution, remaining stationary for 10 seconds and then the microneedles were lifted up at ${10}^{-1}$ m/s. It is noted that in the case of a single microneedle, the penetration depth was $4\times {10}^{-4}$ m, here the penetration depth was only $3\times {10}^{-5}$ m because if the penetration depth was too large, rapid capillary rise would lead the drug solution to reach the roots of the microneedle instantly. The photos in Figures 9(a)-(c) show the three stages of capillary rise between the two cases. It is clear that the interaction between neighboring microneedles can cause a substantial capillary rise at high speeds for an array of microneedles. Figure 10 demonstrates the drug loaded amount for these two cases with three different pulling speeds. The DLV of the three cases for a single microneedle appear to be similar, and apparently the amount on each microneedle in the array is much higher than a single microneedle. For the case with a higher pulling speed, DLV also increase substantially.

Figure 7. Capillary rise of PVA solutions at various concentration for a single microneedle.

Figure 8. Capillary rise for an array of microneedles with two different fluid viscosities.

Figure 9. Comparison of capillary rise between a single microneedle and an array of microneedles.

Figure 10. Comparison of DLV between a single microneedle and an array of microneedles.

4. Conclusions

We have analyzed two approaches for drug loading on microneedles. Dropping is a simple way to apply drug solution on microneedle patches. For a solution with high viscosity and surface tension, the solution will retain on the upper part of the microneedle surface after drying. Once the surface tension of the drug solution is lowered, all the drug solutions will stay at the root area of the microneedle patches, no matter how the difference of viscosity is. This situation may not be favorable for drug delivery into human body.

Dipping is a better method to retain drug solution on the microneedle surfaces. The microneedles would first penetrate into a drug solution pool and then the microneedles were being pulled up. The drug solution that retained on the microneedle surface would form a donut ring. For a single needle, the volume of the donut ring, or the drug loading amount depends on the initial capillary rise before the pulling operation and capillary number. Surface tension is the dominant parameter on the capillary rise. The dependence of DLV on the capillary number is similar to that of flat film provided the initial capillary rise is not significant. High capillary rise would increase the DLV substantially, and higher pulling speed is also an enhancing factor.

As for an array of microneedle, the interaction between microneedles would create a surprisingly fast capillary rising effect. This phenomenon is more significant for drugs solutions with low viscosity and surface tension. Comparison between the results of a single microneedle with an array of microneedles implies that owing to the fast and high capillary rise, the DLV for an array of microneedles can be several times higher than a single microneedle.

We have made an attempt to simulate the dip coating operation for a single and an array of microneedles with some commercial software packages. Owing to the complexity of the system, the numerical predictions on the drug loading amount are much lower than those of experimental findings, although the similar trends are observed. As the effect of viscosity and surface tension of drug solution is clearly shown through this work, the experimentally recorded drug loading amount will be useful toward practical applications of microneedles, especially in MN fabrications and drug dosage control.

More details towards the understanding on the physics of the drug loading process, such as prediction of the dynamic wetting lines and capillary interactions between microneedles, are necessary to better predict the drug loading amount theoretically.

Conflicts of Interest

The authors declare no conflicts of interest.

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