Low-temperature sintering has been pursued ever since the advent of the ceramic and powder metallurgy disciplines. One of the key benefits from low-temperature sintering is fine grain size and thus good mechanical properties. [1][2][3] Another important benefit is the low cost for operation of the heating equipment. Other benefits may include attainment of special functionalities (e.g., optical transparency for polycrystalline oxides), [4,5] avoidance of unwanted reactions between multiple constituents during sintering, [6] and elimination of melting of one of the constituents when cofiring is required. [7] Therefore, a variety of methods have been devised over the years to achieve low-temperature sintering. These methods include high-pressure-assisted sintering, [8,9] spark plasma sintering, [10][11][12] sinter forging, [13,14] sintering with doping or sintering aids, [15][16][17] liquid-phase sintering, [18,19] nanometer-sized powder particle enhanced sintering, [9,20,21] two-step sintering without final-stage grain growth, [22] and phase-transformation-assisted sintering.[23] Here we report a new method based on morphology-enhanced diffusion and driving force to achieve low-temperature sintering. Dense hydroxyapatite (HA) bodies normally require sintering at 1100°C or higher. [24][25][26][27][28][29] The lowest sintering temperature ever reported in the literature is 1000°C with the use of uncalcined nanometer-sized powder particles. [30,31] However, using HA nanorods, we demonstrate in this study that dense (> 99 % of the theoretical) HA nanocrystalline bodies can be attained at 850 or 900°C through morphology-enhanced diffusion and driving force for densification. This new mechanism for increasing the diffusion rate and driving force opens up possibilities to obtain advanced ceramics and composites with enhanced properties or new functionalities via low-temperature sintering. Hydroxyapatite (Ca 10 (PO 4 ) 6 (OH) 2 ) is the main inorganic phase of human hard tissue. It is bioactive and supports bone ingrowth and osteointegration when used in orthopedic, dental, and maxillofacial applications.[32] Although HA has excellent bioactivity, the poor mechanical properties as a bulk material has limited its use to non-load-bearing situations or as a coating on metallic implant surfaces. [33] However, when used as a coating deposited via sol-gel processes, electrochemical deposition, or electrophoretic deposition, HA decomposes to anhydrous calcium phosphates during co-sintering with metallic implants (such as titanium alloys and stainless steels) at 1000°C or higher.[6] Decomposition of HA is undesirable because it results in an enhanced in vitro dissolution rate of HA in simulated physiological solutions. [34,35] To avoid decomposition of HA, the co-sintering temperature is required to be below 950°C, which is substantially lower than the typical sintering temperature of HA, 1100°C.[6] Therefore, to fully utilize the benefit of HA coatings, it is necessary to minimize the HA sintering temperature as much as possible...