Dipolar motions and ionic conduction in an ibuprofen derived ionic liquid.

It was demonstrated that the combination of the almost water insoluble active pharmaceutical ingredient (API) ibuprofen with the biocompatible 1-ethanol-3-methylimidazolium [C2OHMIM] cation of an ionic liquid (IL) leads to a highly water miscible IL-API with a solubility increased by around 5 orders of magnitude. Its phase transformations, as crystallization and glass transition, are highly sensitive to the water content, the latter shifting to higher temperatures upon dehydration. By dielectric relaxation spectroscopy the dynamical behavior of anhydrous [C2OHMIM][Ibu] and with 18.5 and 3% of water content (w/w) was probed from well below the calorimetric glass transition (Tg) up to the liquid state. Multiple reorientational dipolar processes were detected which become strongly affected by conductivity and electrode polarization near above Tg. Therefore [C2OHMIM][Ibu] exhibits mixed behavior of a conventional molecular glass former and an ionic conductor being analysed in this work through conductivity, electrical modulus and complex permittivity. The dominant process, σα-process, originates by a coupling between both charge transport and dipolar mechanisms. The structural relaxation times were derived from permittivity analysis and confirmed by temperature modulated differential scanning calorimetry. The temperature dependence of the ß-secondary relaxation is coherent with a Johari-Goldstein (ßJG) process as detected in conventional glass formers.

Molecular mobility of amorphous S-flurbiprofen: a dielectric relaxation spectroscopy approach.

Amorphous S-flurbiprofen was obtained by the melt quench/cooling method. Dielectric measurements performed in the isochronal mode, conventional and temperature modulated differential scanning calorimetry (TMDSC) studies showed a glass transition, recrystallization, and melting. The different parameters characterizing the complex molecular dynamics of amorphous S-flurbiprofen that can have influence on crystallization and stability were comprehensively characterized by dielectric relaxation spectroscopy experiments (isothermal mode) covering a wide temperature (183 to 408 K) and frequency range (10(-1) to 10(6) Hz): width of the α-relaxation (ßKWW), temperature dependence of α-relaxation times (τα), fragility index (m), relation of the α-relaxation with the ß-secondary relaxation, and the breakdown of the Debye-Stokes-Einstein (DSE) relationship between the structural relaxation time and dc-conductivity (σdc) at deep undercooling close to Tg. The ß-relaxation, observed in the glassy as well as in the supercooled state was identified as the genuine Johari-Goldstein process, attributed to localized motions and regarded as the precursor of the α-relaxation as suggested in the coupling model. A separation of about 6 decades between the α- and ß-relaxation was observed at Tg; this decoupling decreased on increasing temperature, and both processes merged at Tαß = 295 K. The temperature dependence of the α-relaxation time, τα, was described by two Vogel-Fulcher-Tammann-Hesse equations, which intercept at a crossover temperature, TB = 290 K, close to the splitting temperature between the α- and ß-relaxation. From the low temperature VFTH equation, a Tg(DRS) = 265.2 was estimated (at τα =100 s) in good agreement with the calorimetric value (Tg,onset,TMDSC = 265.6 K), and a fragility or steepness index m = 113 was calculated allowing to classify S-flurbiprofen as a fragile glass former. The α-relaxation spectra were found to be characterized by a relatively large degree of nonexponentiality (ßKWW = 0.52). A breakdown of the DSE log10 σdc - log10 τ relation was observed revealing an enhancement of translational ionic motions in comparison with the orientational molecular motions as the glass transition temperature Tg is approached from above.

A stable amorphous statin: solid-state NMR and dielectric studies on dynamic heterogeneity of simvastatin.

Statins have been widely used as cholesterol-lowering agents. However, low aqueous solubility of crystalline statins and, consequently, reduced biovailability require seeking for alternative forms and formulations to ensure an accurate therapeutic window. The objective of the present study was to evaluate the stability of amorphous simvastatin by probing molecular dynamics using two nondestructive techniques: solid-state NMR and dielectric relaxation spectroscopy. Glassy simvastatin was obtained by the melt quench technique. (13)C cross-polarization/magic-angle-spinning (CP/MAS) NMR spectra and (1)H MAS NMR spectra were obtained from 293 K up to 333 K (Tg ≈ 302 K). The (13)C spin-lattice relaxation times in the rotating frame, T1ρ, were measured as a function of temperature, and the correlation time and activation energy data obtained for local motions in different frequency scales revealed strong dynamic heterogeneity, which appears to be essential for the stability of the amorphous form of simvastatin. In addition, the (1)H MAS measurements presented evidence for mobility of the hydrogen atoms in hydroxyl groups which was assigned to noncooperative secondary relaxations. The complex dielectric permittivity of simvastatin was monitored in isochronal mode at five frequencies (from 0.1 to 1000 kHz), by carrying out a heating/cooling cycle allowing to obtain simvastatin in the supercooled and glassy states. The results showed that no dipolar moment was lost due to immobilization, thus confirming that no crystallization had taken place. Complementarily, the present study focused on the thermal stability of simvastatin using thermogravimetric analysis while the thermal events were followed up by differential scanning calorimetry and dielectric relaxation spectroscopy. Overall, the results confirm that the simvastatin in the glass form reveals a potential use in the solid phase formulation on the pharmaceutical industry.

Vibrational and structural properties of amorphous n-butanol: a complementary Raman spectroscopy and X-ray diffraction study.

Raman spectroscopy and X-ray diffraction experiments were performed in the liquid, undercooled liquid, and glassy states of n-butanol. Clear correlated signatures are obtained below the melting temperature, from both temperature dependences of the low-wavenumber vibrational excitations and the intermediate-range order characterized by a prepeak detected in the different amorphous states. It was found that these features are related to molecular associations via strong hydrogen bonds, which preferentially develop at low temperature, and which are not compatible with the long-range order of the crystal. This study provides information on structural heterogeneities developing in hydrogen-bonded liquids, associated to the undercooled regime and the inherent glass transition. The analysis of the isothermal abortive crystallization, 2 K above the glass transition temperature, has given the opportunity to analyze the early stages of the crystallization and to describe the origin of the frustration responsible for an uncompleted crystallization.

Exploration of the physical states of riboflavin (free base) by mechanical milling.

Amorphous riboflavin (free base) could be produced for the first time via high energy ball milling of a commercial crystalline form (Form I). Importantly, this solid state amorphization process allowed to circumvent chemical degradation occurring during melting as well as the lack of suitable solvents, which are required for amorphization via spray- or freeze-drying. The amorphous state of riboflavin was thoroughly characterized, revealing a complex recrystallization pattern upon heating, involving two enantiotropic polymorphic forms (II and III) and a dihydrate. The glass transition temperature (Tg) and heat capacity (Cp) jump of the amorphous form were determined as 144 °C and 0.68 J/g/°C. Moreover, the relative physical stability of the different physical states has been elucidated, e.g., at room temperature: I > II > III. The following rank order was observed for the dissolution rates in water at 37 °C during the first 4 h: amorphous > III ≈ II > I. Afterwards, a dihydrate crystallized from the solutions of amorphous and metastable crystalline riboflavin forms, the solubility of which was well above the solubility of the stable FormI.

Drug release from PLGA microparticles can be slowed down by a surrounding hydrogel.

This study aimed to evaluate and better understand the potential impact that a layer of surrounding hydrogel (mimicking living tissue) can have on the drug release from PLGA microparticles. Ibuprofen-loaded microparticles were prepared with an emulsion solvent extraction/evaporation method. The drug loading was about 48%. The surface of the microparticles appeared initially smooth and non-porous. In contrast, the internal microstructure of the particles exhibited a continuous network of tiny pores. Ibuprofen release from single microparticles was measured into agarose gels and well-agitated phosphate buffer pH 7.4. Optical microscopy, scanning electron microscopy, differential scanning calorimetry, X-ray powder diffraction, and X-ray µCT imaging were used to characterize the microparticles before and after exposure to the release media. Importantly, ibuprofen release was much slower in the presence of a surrounding agarose gel, e.g., the complete release took two weeks vs. a few days in well agitated phosphate buffer. This can probably be attributed to the fact that the hydrogel sterically hinders substantial system swelling and, thus, slows down the related increase in drug mobility. In addition, in this particular case, the convective flow in agitated bulk fluid likely damages the thin PLGA layer at the microparticles' surface, giving the outer aqueous phase more rapid access to the inner continuous pore network: Upon contact with water, the drug dissolves and rapidly diffuses out through a continuous network of water-filled channels. Without direct surface access, most of the drug "has to wait" for the onset of substantial system swelling to be released.

Evidence of transient amorphization during the polymorphic transformation of sorbitol induced by milling.

In this paper, we show that the polymorphic transformation γ â†’ α of sorbitol upon milling involves a transient amorphization of the material. This could be done by comilling sorbitol with a high Tg amorphous material (Hydrochlorothiazide, Tg = 115 °C) to stabilize any transient amorphous fractions of sorbitol through the formation of a molecular alloy. The results indicate that for large sorbitol concentration (50%), the comilling leads to a heterogeneous mixture made of sorbitol crystallites in the form α embedded into an amorphous molecular alloy sorbitol / HCT. Interestingly, the kinetic investigation of this transformation reveals that these two components are not produced simultaneously. On the contrary, they are produced one after the other, during two distinct consecutive stages. The first stage concerns the formation of the amorphous alloy while the second one concerns the polymorphic transformation γ â†’ α of the fraction of crystalline sorbitol not involved in the alloy. These results clearly indicate that the polymorphic transformation of sorbitol upon milling results from the recrystallization of a transient amorphous state generated by the mechanical shocks. The investigations were mainly performed by calorimetry and powder X-ray diffraction.

The melting of glucose.

Several sugars are known to undergo a spontaneous liquefaction below their reputed melting point (Tm), but the origin of this apparent melting is not yet clearly understood. In this paper we address this puzzling behavior in the particular case of the crystalline forms of glucose: Gα and Gß, involving respectively the glucose-α and glucose-ß anomers. We show in particular that the spontaneous melting below their reputed melting point Tm (∼151 °C for Gα and ∼156 °C for Gß) corresponds to a horizontal displacement of the system in the eutectic phase diagram of the anomeric mixture glucose-α / glucose-ß. This displacement is associated with mutarotation in the liquid which, in turn, induces additional liquefaction of the remaining crystal. This feedback loop creates a vicious circle which stops when the mixture reaches the liquidus branch, i.e. when the liquefaction is total. It is also shown that this behavior becomes more complex on approaching the eutectic temperature Te (120 °C). Just above Te, the liquefaction process is followed by a recrystallization leading to the crystalline form Gß. On the other hand, just below Te, the spontaneous liquefaction process stops as no melting is expected whatever the anomeric composition.

Long term behavior of dexamethasone-loaded cochlear implants: In vitro & in vivo.

The aim of this study was to better understand the long term behavior of silicone-based cochlear implants loaded with dexamethasone: in vitro as well as in vivo (gerbils). This type of local controlled drug delivery systems offers an interesting potential for the treatment of hearing loss. Because very long release periods are targeted (several years/decades), product optimization is highly challenging. Up to now, only little is known on the long term behavior of these systems, including their drug release patterns as well as potential swelling or shrinking upon exposure to aqueous media or living tissue. Different types of cylindrical, cochlear implants were prepared by injection molding, varying their dimensions (being suitable for use in humans or gerbils) and initial drug loading (0, 1 or 10%). Dexamethasone release was monitored in vitro upon exposure to artificial perilymph at 37 °C for >3 years. Optical microscopy, X-ray diffraction and Raman imaging were used to characterize the implants before and after exposure to the release medium in vitro, as well as after 2 years implantation in gerbils. Importantly, in all cases dexamethasone release was reliably controlled during the observation periods. Diffusional mass transport and limited drug solubility effects within the silicone matrices seem to play a major role. Initially, the dexamethasone is homogeneously distributed throughout the polymeric matrices in the form of tiny crystals. Upon exposure to aqueous media or living tissue, limited amounts of water penetrate into the implant, dissolve the drug, which subsequently diffuses out. Surface-near regions are depleted first, resulting in an increase in the apparent drug diffusivity with time. No evidence for noteworthy implant swelling or shrinkage was observed in vitro, nor in vivo. A simplified mathematical model can be used to facilitate drug product optimization, allowing the prediction of the resulting drug release rates during decades as a function of the implant's design.

Dexamethasone-loaded cochlear implants: How to provide a desired "burst release".

Cochlear implants containing iridium platinum electrodes are used to transmit electrical signals into the inner ear of patients suffering from severe or profound deafness without valuable benefit from conventional hearing aids. However, their placement is invasive and can cause trauma as well as local inflammation, harming remaining hair cells or other inner ear cells. As foreign bodies, the implants also induce fibrosis, resulting in a less efficient conduction of the electrical signals and, thus, potentially decreased system performance. To overcome these obstacles, dexamethasone has recently been embedded in this type of implants: into the silicone matrices separating the metal electrodes (to avoid short circuits). It has been shown that the resulting drug release can be controlled over several years. Importantly, the dexamethasone does not only act against the immediate consequences of trauma, inflammation and fibrosis, it can also be expected to be beneficial for remaining hair cells in the long term. However, the reported amounts of drug released at "early" time points (during the first days/weeks) are relatively low and the in vivo efficacy in animal models was reported to be non-optimal. The aim of this study was to increase the initial "burst release" from the implants, adding a freely water-soluble salt of a phosphate ester of dexamethasone. The idea was to facilitate water penetration into the highly hydrophobic system and, thus, to promote drug dissolution and diffusion. This approach was efficient: Adding up to 10% dexamethasone sodium phosphate to the silicone matrices substantially increased the resulting drug release rate at early time points. This can be expected to improve drug action and implant functionality. But at elevated dexamethasone sodium phosphate loadings device swelling became important. Since the cochlea is a tiny and sensitive organ, a potential increase in implant dimensions over time must be limited. Hence, a balance has to be found between drug release and implant swelling.

Polymorphism and stability of ibuprofen/nicotinamide cocrystal: The effect of the crystalline synthesis method.

The development over the past decade of design strategies for cocrystal preparation have led to numerous methods for the synthesis of cocrystal without take care of their influence on the precise structure and stability of cocrystalline states. On the other hand the mechanism of cocrystal formation remains widely unclear, especially the identification of the type of interactions mostly responsible for the cocrystalline stability. The present study focuses on the influence of the crystalline synthesis method on the polymorphism of cocrystals was analyzed from the preparation of S-ibuprofen/nicotinamide and RS-ibuprofen/nicotinamide cocrystals by co-milling, slow solvent evaporation and crystallization from the melt. X-ray diffraction and Raman spectroscopy experiments have shown that the polymorphic form of the cocrystals obtained by recrystallization from the melt (Form A) is different from that prepared by milling and by slow evaporation in solution (Form B). It was shown that both isothermal and non-isothermal recrystallizations from the melt blending are observed via a transient metastable micro/nano structure of form A. Additionally, it was observed that form A transforms into Form B upon heating via very weak changes in the hydrogen bond network. The crystallization in form A from the melt, instead of form B by other methods, was explained by the difficulty to form a supramolecular organization too far energetically from that existing in the melt. This study shows the crucial role of supramolecular H-bonding on the formation mechanism of cocrystals and how does the synthesis method of cocrystals change the supramolecular organization and the related structure of cocrystals.

Interest of molecular/crystalline dispersions for the determination of solubility curves of drugs into polymers.

We present here a method to increase the dissolution rate of drugs into polymers in order to make easier and faster the determination of the solubility curves of these mixtures. The idea is to prepare molecular/crystalline dispersions (MCD) where the drug is dispersed into the polymer, partly at the molecular level and partly in the form of small crystallites. We show that this particular microstructure greatly increases the dissolution rate of crystallites since: (1) The molecular dispersion has a plasticizing effect which greatly increases the molecular mobility in the amorphous matrix. (2) The fine crystallite dispersion in the matrix strongly reduces the distances over which the drug molecules have to diffuse to invade homogeneously the polymer by dissolution. MCD are here obtained by combining solid-state co-amorphization by high energy mechanical milling and then recrystallization by annealing under a plasticizing atmosphere. We have used MCD to determine the solubility lines of the two polymorphic forms (I and II) of sulindac into PVP. The investigations have been performed mainly by DSC and powder x-ray diffraction.

Mechanistic explanation of the (up to) 3 release phases of PLGA microparticles: Diprophylline dispersions.

The aim of this study was to better understand the root causes for the (up to) 3 drug release phases observed with poly (lactic-co-glycolic acid) (PLGA) microparticles containing diprophylline particles: The 1st release phase ("burst release"), 2nd release phase (with an "about constant release rate") and 3rd release phase (which is again rapid and leads to complete drug exhaust). The behavior of single microparticles was monitored upon exposure to phosphate buffer pH 7.4, in particular with respect to their drug release and swelling behaviors. Diprophylline-loaded PLGA microparticles were prepared with a solid-in-oil-in-water solvent extraction/evaporation method. Tiny drug crystals were rather homogeneously distributed throughout the polymer matrix after manufacturing. Batches with "small" (63 µm), "medium-sized" (113 µm) and "large" (296 µm) microparticles with a practical drug loading of 5-7% were prepared. Importantly, each microparticle releases the drug "in its own way", depending on the exact distribution of the tiny drug crystals within the system. During the burst release, drug crystals with direct surface access rapidly dissolve. During the 2nd release phase tiny drug crystals (often) located in surface near regions which undergo swelling, are likely released. During the 3rd release phase, the entire microparticle undergoes substantial swelling. This results in high quantities of water present throughout the system, which becomes "gel-like". Consequently, the drug crystals dissolve, and the dissolved drug molecules rather rapidly diffuse through the highly swollen polymer gel.

PLGA implants: How Poloxamer/PEO addition slows down or accelerates polymer degradation and drug release.

The aim of this study was to evaluate the impact of the addition of small amounts of hydrophilic polymers (Poloxamer 188 and PEO 200kDa) to PLGA-based implants loaded with prilocaine. Special emphasis was placed on the importance of the type of preparation technique: direct compression of milled drug-polymer powder blends versus compression of drug loaded microparticles (prepared by spray-drying). The implants were thoroughly characterized before and upon exposure to phosphate buffer pH7.4, e.g. using optical and scanning electron microscopy, X-ray diffraction, DSC and GPC. Interestingly, the addition of Poloxamer/PEO to the PLGA implants had opposite effects on the resulting drug release kinetics, depending on the type of preparation method: in the case of implants prepared by compression of milled drug-polymer powder blends, drug release was accelerated, whereas it was slowed down when the implants were prepared by compression of drug loaded PLGA microparticles. These phenomena could be explained by the swelling/disintegration behavior of the implants upon exposure to the release medium. Systems consisting of compressed microparticles remained intact and autocatalytic effects were of major importance. The presence of a hydrophilic polymer facilitated water penetration into these devices, slowing down PLGA degradation and drug release. In contrast, implants consisting of compressed drug-polymer powder blends rapidly (at least partially) disintegrated and autocatalysis was much less important. In these cases, the addition of a hydrophilic polymer facilitated ester bond cleavage, leading to accelerated PLGA degradation and drug release.

Metastability release of the form alpha of trehalose by isothermal solid state vitrification.

Kinetic investigations of the polymorphic form alpha of anhydrous trehalose have been performed below its apparent melting temperature (Tm) by differential scanning calorimetry (DSC) and X-ray diffraction. The results reveal a spontaneous isothermal vitrification process which indicates that the phase alpha is in a very unusual superheating situation. This behavior has been attributed to the fact that the effective melting temperature (Tm(eff)) of the phase alpha is likely to be located far below the glass transition temperature (Tg) of this compound. The high viscosity of the liquid trehalose between Tm(eff) and Tg is thus invoked to explain the long lifetime of the phase alpha in this temperature range.

Towards a better understanding of the different release phases from PLGA microparticles: Dexamethasone-loaded systems.

Dexamethasone-loaded, poly(lactic-co-glycolic acid) (PLGA) microparticles were prepared using an oil-in-water solvent extraction/evaporation method. The drug loading was varied from 2.4 to 61.9%, keeping the mean particle size in the range of 52-61µm. In vitro drug release was characterized by up to 3 phases: (1) an (optional) initial burst release, (2) a phase with an about constant drug release rate, and (3) a final, again rapid, drug release phase. The importance and durations of these phases strongly depended on the initial drug loading. To better understand the underlying mass transport mechanisms, the microparticles were thoroughly characterized before and after exposure to the release medium. The initial burst release seems to be mainly due to the dissolution of drug particles with direct access to the microparticles' surface. The extent of the burst was negligible at low drug loadings, whereas it exceeded 60% at high drug loadings. The second release phase seems to be controlled by limited drug solubility effects and drug diffusion through the polymeric systems. The third drug release phase is likely to be a consequence of substantial microparticle swelling, leading to a considerable increase in the systems' water content and, thus, fundamentally increased drug mobility.

Ear Cubes for local controlled drug delivery to the inner ear.

A new type of advanced drug delivery systems is proposed: Miniaturized implants, which can be placed into tiny holes drilled into (or close to) the oval window. They consist of two parts: 1) A cylinder, which is inserted into the hole crossing the oval window. The cylinder (being longer than the depth of the hole) is partly located within the inner ear and surrounded by perilymph. This provides direct access to the target site, and at the same time assures implant fixation. 2) A cuboid, which is located in the middle ear, serving as a drug reservoir. One side of the cuboid is in direct contact with the oval window. Drug release into the cochlea occurs by diffusion through the cylindrical part of the Ear Cubes and by diffusion from the cuboid into and through the oval window. High precision molds were used to prepare two differently sized Ear Cubes by injection molding. The miniaturized implants were based on silicone and loaded with different amounts of dexamethasone (10 to 30 % w/w). The systems were thoroughly characterized before and upon exposure to artificial perilymph at 37°C. Importantly, drug release can effectively be controlled and sustained during long time periods (up to several years). Furthermore, the implants did not swell or erode to a noteworthy extent during the observation period. Drug diffusion through the polymeric matrix, together with limited dexamethasone solubility effects, seem to control the resulting drug release kinetics, which can roughly be estimated using mathematical equations derived from Fick's second law. Importantly, the proposed Ear Cubes are likely to provide much more reliable local long term drug delivery to the inner ear compared to liquid or semi-solid dosage forms administered into the middle ear, due to a more secured fixation. Furthermore, they require less invasive surgeries and can accommodate higher drug amounts compared to intracochlear implants. Thus, they offer the potential to open up new horizons for innovative therapeutic strategies to treat inner ear diseases and disorders.

Does PLGA microparticle swelling control drug release? New insight based on single particle swelling studies.

The aim of this study was to better understand the mass transport mechanisms controlling drug release from PLGA microparticles. New insight was gained based on the experimental monitoring of single microparticle swelling. An oil-in-water (O/W) solvent extraction/evaporation method was used to prepare ketoprofen-loaded microparticles, varying the initial drug loading from 0.6 to 45.2%. Importantly, the microparticle size was kept about constant. At low ketoprofen loadings, the release patterns were clearly tri-phasic: an initial burst release was followed by a period with an about constant release rate and a final (again rapid) drug release phase. With increasing initial drug content the onset of the third release period was shifted to earlier time points. At even higher drug loadings, the release patterns became more or less bi- or mono-phasic. Interestingly, all types of microparticles showed substantial swelling after a lag-time, which coincided with the onset of the third (and again rapid) drug release phase at low loadings and proceeded it by 1 or 2d at higher drug loadings. The substantial microparticle swelling set on as soon as a critical PLGA molecular weight was reached (around 20 kDa). Thus, the onset of the third drug release phase from the PLGA microparticles might be explained as follows: once the macromolecules are sufficiently short, substantial amounts of water penetrate into the system, significantly increasing the mobility of the drug within the microparticles and resulting in increased drug release rates.

Solid state NMR and DSC methods for quantifying the amorphous content in solid dosage forms: an application to ball-milling of trehalose.

The purpose of this study was to determine quantitatively the amorphous fraction in crystalline-amorphous powder mixtures of trehalose, in order to assess the ability of the (13)C NMR technique for quantitative amorphous characterization. The NMR method is described in detail and its accuracy is compared to that of the DSC technique. Amorphous trehalose was prepared by mechanical milling. Samples with different amorphous fractions were prepared by physical mixing of purely amorphous and purely crystalline powders. The results reveal a close correlation between the imposed compositions of the physical mixtures and those determined by NMR and DSC, indicating that both are useful and accurate methods for compositional characterization of powders. The NMR method is then used to determine the evolution of the amorphous fraction in a trehalose powder, during a milling procedure which ultimately leads to a fully amorphous state.

Mechanism of solid state amorphization of glucose upon milling.

Crystalline α-glucose is known to amorphize upon milling at -15 °C while it remains structurally invariant upon milling at room temperature. We have taken advantage of this behavior to compare the microstructural evolutions of the material in both conditions in order to identify the essential microstructural features which drive the amorphization process upon milling. The investigations have been performed by differential scanning calorimetry and by powder X-ray diffraction. The results indicate that two different amorphization mechanisms occur upon milling: an amorphization at the surface of crystallites due to the mechanical shocks and a spontaneous amorphization of the crystallites as they reach a critical size, which is close to 200 Å in the particular case of α-glucose.